WO2011026148A1 - Analyte monitoring system and methods for managing power and noise - Google Patents
Analyte monitoring system and methods for managing power and noise Download PDFInfo
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- WO2011026148A1 WO2011026148A1 PCT/US2010/047413 US2010047413W WO2011026148A1 WO 2011026148 A1 WO2011026148 A1 WO 2011026148A1 US 2010047413 W US2010047413 W US 2010047413W WO 2011026148 A1 WO2011026148 A1 WO 2011026148A1
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K1/00—Details of thermometers not specially adapted for particular types of thermometer
- G01K1/02—Means for indicating or recording specially adapted for thermometers
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0002—Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K13/00—Thermometers specially adapted for specific purposes
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
- A61B2560/0204—Operational features of power management
- A61B2560/0209—Operational features of power management adapted for power saving
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
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- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/12—Condition responsive control
Definitions
- Diabetes Mellitus is an incurable chronic disease in which the body does not produce or properly utilize insulin.
- Insulin is a hormone produced by the pancreas that regulates blood sugar (glucose).
- glucose blood sugar
- the pancreas does not produce sufficient insulin (a condition known as Type I Diabetes) or does not properly utilize insulin (a condition known as Type II Diabetes)
- Type I Diabetes a condition known as Type I Diabetes
- Type II Diabetes a condition known as Type II Diabetes
- diabetes suffering from diabetes cause long-term, serious complications. Some of these complications include blindness, kidney failure, and nerve damage. Additionally, it is known that diabetes is a factor in accelerating cardiovascular diseases such as atherosclerosis (hardening of the arteries), leading to stroke, coronary heart disease, and other diseases. Accordingly, one important and universal strategy in managing diabetes is to control blood glucose levels.
- the first step in managing blood glucose levels is testing and monitoring blood glucose levels by using conventional techniques, such as drawing blood samples, applying the blood to a test strip, and determining the blood glucose level using colorimetric, electrochemical, or photometric test meters.
- Another more recent technique for monitoring blood glucose levels is by using a continuous or automatic glucose monitoring system.
- continuous analyte monitoring systems employ an insertable or implantable sensor, which - - continuously detects and monitors blood glucose levels. These blood glucose levels may then be displayed to a user to assist the user in managing the user's diabetes.
- the continuous analyte monitoring system such as a receiver
- data corresponding to the monitored blood glucose levels may be lost or become corrupt if the receiver of the analyte monitoring system shuts down due to lack of power in a rechargeable power source of the receiver.
- noise produced by various components of the analyte monitoring system may interfere with a signal that conveys the monitored blood glucose levels.
- Embodiments described herein relate to systems and methods for selectively disabling components of an analyte monitoring device based on a percentage of power remaining in a power source of the analyte monitoring device.
- the analyte monitoring device is configured to determine a temperature level of the power source of the analyte monitoring device, determine a level of power remaining in the power source of the analyte monitoring device, and selectively deactivate at least one component of the analyte monitoring device when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
- Also disclosed herein are methods and systems for reducing noise caused by components of the analyte monitoring device during data transmission and/or reception.
- FIG. 1 illustrates a block diagram of a data monitoring and management system for according to embodiments of the present disclosure
- FIG. 2 is a block diagram of a receiver unit according to embodiments of the present disclosure
- FIG. 3 is a block diagram of a battery management feature of a receiver according to embodiments of the present disclosure.
- FIG. 4 is a flow chart illustrating a method for determining whether a receiver is to enter a play dead mode according to embodiments of the present disclosure
- FIG. 5 is a state diagram of battery charge and discharge features of a receiver according to embodiments of the present disclosure.
- FIG. 6 illustrates temperature and voltage conditions of a receiver entering a play dead mode according to embodiments of the present disclosure
- FIG. 7 is a block diagram of a portion of a receiver according to embodiments of the present disclosure.
- FIG. 8 is a flow chart illustrating a method for reducing noise according to embodiments of the present disclosure.
- FIG. 9 is a state diagram of a power mode of a receiver according to
- analyte monitoring system Various exemplary embodiments of the analyte monitoring system and methods of the disclosure are described in further detail below. Although the disclosure is described primarily with respect to a glucose monitoring system, each aspect of the disclosure is not intended to be limited to the particular embodiment so described. Accordingly, it is to be understood that such description should not be construed to limit the scope of the disclosure, and it is to be understood that the analyte monitoring system can be configured to monitor a variety of analytes, as described below.
- FIG. 1 illustrates a data monitoring and management system such as, for example, analyte (e.g., glucose) monitoring system 100 in accordance with embodiments of the present disclosure.
- the analyte monitoring system 100 may be a continuous monitoring system, a semi-continuous monitoring system, a discrete monitoring system or an on-demand monitoring system.
- the analyte monitoring system 100 includes a sensor 101, a transmitter unit 102 coupleable to the sensor 101, and a primary receiver unit 104 which is configured to communicate with the transmitter unit 102 via a bi-directional communication link 103.
- the primary receiver unit 104 may be further configured to transmit data to a data processing terminal 105 for evaluating the data received by the primary receiver unit 104.
- the data processing terminal 105 in one embodiment may be configured to receive data directly from the transmitter unit 102 via a communication link which may optionally be configured for bi-directional - - communication.
- transmitter unit 102 and/or receiver unit 104 may include a transceiver.
- FIG. 1 Also shown in FIG. 1 is an optional secondary receiver unit 106 which is operatively coupled to the communication link and configured to receive data transmitted from the transmitter unit 102. Moreover, as shown in the Figure, the secondary receiver unit 106 is configured to communicate with the primary receiver unit 104 as well as the data processing terminal 105. Indeed, the secondary receiver unit 106 may be configured for bidirectional wireless communication with each or one of the primary receiver unit 104 and the data processing terminal 105. In one embodiment of the present disclosure, the secondary receiver unit 106 may be configured to include a limited number of functions and features as compared with the primary receiver unit 104.
- the secondary receiver unit 106 may be configured substantially in a smaller compact housing or embodied in a device such as a wrist watch, pager, mobile phone, Personal Digital Assistant (PDA), for example.
- the secondary receiver unit 106 may be configured with the same or substantially similar functionality as the primary receiver unit 104.
- the receiver unit may be configured to be used in conjunction with a docking cradle unit, for example for one or more of the following or other functions: placement by bedside, for re-charging, for data management, for night time monitoring, and/or bidirectional communication device.
- sensor 101 may include two or more sensors, each configured to communicate with transmitter unit 102.
- transmitter unit 102, communication link 103, and data processing terminal 105 are shown in the embodiment of the analyte monitoring system 100 illustrated in FIG. 1, in certain embodiments, the analyte monitoring system 100 may include one or more sensors, multiple transmitter units 102, communication links 103, and data processing terminals 105.
- the analyte monitoring system 100 may be a continuous monitoring system, or semi- continuous, or a discrete monitoring system. In a multi-component environment, each device is configured to be uniquely identified by each of the other devices in the system so that communication conflict is readily resolved between the various components within the analyte monitoring system 100.
- the senor 101 is physically positioned in or on the body of a user whose analyte level is being monitored.
- the sensor 101 may be configured to continuously sample the analyte level of the user and convert the sampled analyte level into a corresponding data signal for transmission by the transmitter unit 102.
- the transmitter unit 102 may be physically coupled to the sensor 101 so that both devices are integrated in a single housing and positioned on the user's body.
- the transmitter unit 102 may perform data processing such as filtering and encoding on data signals and/or other functions, each of which corresponds to a sampled analyte level of the user, and in any event transmitter unit 102 transmits analyte information to the primary receiver unit 104 via the communication link 103. Additional detailed description of the continuous analyte monitoring system, its various components including the functional descriptions of the transmitter are provided in but not limited to U.S. Patent Nos. 6,134,461, 6,175,752, 6,121,611, 6,560,471, and
- FIG. 2 is a block diagram of a receiver 200 according to embodiments of the present disclosure.
- receiver 200 may be the primary receiver unit 104 (FIG. 1) or the secondary receiver unit 106 as described above.
- the receiver 200 includes an analyte test strip interface 201, (e.g., blood glucose test strip port), a radio frequency (RF) receiver 202, a user input mechanism 203 (e.g., one or more keys of a keypad, a touch- sensitive screen, a voice-activated input command unit etc.), a temperature detection section 204, and a clock 205, each of which is operatively coupled to a receiver processor 207.
- RF radio frequency
- the receiver 200 also includes a power supply 206, such as, for example, a rechargeable battery, operatively coupled to a power conversion and monitoring section 208. Further, the power conversion and monitoring section are also coupled to the receiver processor 207. A receiver serial communication section 209, and an output 210, such as, for example a display, are each operatively coupled to the receiver processor 207.
- the analyte monitoring system 100 is a continuous glucose monitoring system
- the test strip interface 201 includes a glucose level testing portion to manually receive a glucose test strip to determine the glucose level of a blood sample applied to the test strip.
- the receiver 200 may be configured to output blood glucose information determined from the test strip on the display. Additionally, the test strip can be used to calibrate a sensor such as, for example sensor 101.
- the receiver 200 includes two sections.
- the first section is an analog interface section that is configured to communicate with the transmitter unit 102 via the communication link 103.
- the analog interface section may include an RF receiver and an antenna for receiving and amplifying the data signals from the transmitter unit 102, which are thereafter, demodulated with a local oscillator and filtered through a band-pass filter.
- the second section of the receiver is a data processing section which is configured to process the data signals received from the transmitter unit 102 such as by performing data decoding, error detection and correction, data clock generation, and data bit recovery.
- various data processing functionalities are executed by the receiver 200 such as, for example, calibration of analyte levels received from the sensor 101 and the transmitter unit 102 and techniques for managing power and noise of the analyte monitoring system 100, based on the periodic transmission of data from the transmitter unit 102.
- a receiver 200 has an operating mode which prevents a user from operating the receiver 200 or suspends or deactivates certain
- Such conditions may include a low battery level of the receiver 200, such as, for example, a low battery level that prompts hardware shutdown.
- Other conditions may include low or high operating temperatures of the receiver 200 that may cause data corruption or erroneous behavior if the receiver 200 were to continue operating under such conditions. As will be described in greater detail below, this suspended
- play dead mode the receiver 200 continues to run a main clock and perform certain internal operations to keep desired data updated and current.
- Such operations and/or data may include operations and data corresponding to sensor life, calibration, timing of the receipt of data packets and the like.
- certain operations remain active, other operations of the receiver 200 are suspended.
- the operations that are suspended include writing data to memory, such as, for example a flash memory of the receiver 200, outputting sounds such as alarms, tones and/or other notifications, displaying data on a display unit, or communicating commands to remotely controlled device, such as, for example, a pump.
- one or more processors of the receiver 200 utilize a battery monitoring algorithm which performs a charge counting routine when determining whether to enter the play dead mode. More specifically, the charge counting routine in certain embodiments includes determining an estimate corresponding to an amount of battery charge available on a well-functioning battery during the lifecycle of the receiver 200. In certain embodiments, the battery monitoring algorithm takes into account variations in batteries from different manufacturers as well as an estimate of degradation of the battery capacity due to aging over the lifetime of the battery.
- the battery monitoring algorithm and associated battery management and charging functionalities of the receiver 200 is performed by power management module 300.
- the power management module 300 is equivalent to power conversion and monitoring section 208 (FIG. 2) and includes a battery charger 310 and a fuel gauge 320.
- the power management module 300 is configured to prevent a power supply 206 (e.g., rechargeable battery) of the receiver 200 from charging when a detected temperature of the receiver 200 and/or the battery is not in safe operating range.
- the power management module 300 is configured to prevent the battery from being continuously charged after the battery has been charging for a maximum charging period (e.g., more than about 3 hours).
- the power management module 300 when the remaining power level of a battery of the receiver 200 reaches a predetermined minimum threshold level, the power management module 300 is configured to cut off power to one or more processors of the receiver 200, which may suspend or deactivate various functionalities of the receiver 200.
- the receiver 200 may have a user interface processor 330
- the user interface components 340 may include, one or more buttons disposed on a housing of the receiver 200, a display, such as, for example a touch sensitive display, a sound synthesizer, a vibration component, and/or a backlight.
- a display such as, for example a touch sensitive display, a sound synthesizer, a vibration component, and/or a backlight.
- the receiver may include additional user interface components configured to enable a user to interact with the receiver 200.
- the user interface processor 330 is configured to interact with the various user interface components 340 including updating the display of the receiver 200, processing received glucose data, maintaining a log of historical information, operating the sound synthesizer and/or the vibration component, and/or interface with the power management module 300.
- the receiver 200 may also include glucose engine processor 350 configured to receive and process analyte data received from a transmitter, such as, for example, transmitter unit 102 (FIG. 1) and/or data received from a test strip port 360.
- a transmitter such as, for example, transmitter unit 102 (FIG. 1)
- test strip port 360 may be equivalent to test strip interface 201 (FIG. 2).
- one or more operations or functionalities of the receiver 200 that are controlled by each of the above mentioned processors may be deactivated or suspended when entering the play dead mode.
- the battery monitoring algorithm discussed above incorporates several design constraints and considerations.
- one consideration is discharge of the battery of the receiver 200.
- the battery of the receiver 200 is a lithium-ion battery.
- the power management module 300 may be configured to cut or reduce power to one or more processors of the receiver 200 when the battery voltage drops below a certain voltage minimum threshold (e.g., about 3.3V).
- the battery when the voltage remaining in the battery drops below a certain threshold, for example about 3.6V, the battery is considered an empty battery and the power management module 300 reduces or cuts power to one or more of the processors to conserve the remaining battery power.
- a certain threshold for example about 3.6V
- the power management module 300 when the power management module 300 cuts power from the battery, certain functionalities of the receiver 200 are disabled while other functionalities of the receiver 200 may remain active.
- one or more processors of the receiver 200 may be configured to determine which components and/or operations (e.g. writing to flash memory, updating a display, etc.) controlled by a particular processor are consuming the most power. The processor may then deactivate one or more operations and/or components that are consuming the most power while other operations and/or components controlled by that processor remain active.
- the user interface processor 330 may control a display and a light source of the receiver 200.
- the user interface processor 350 may determine that continued operation of the light source will require more power than operation of the display. As such, the light source will be deactivated until the battery of the receiver 200 is recharged, but the display remains active.
- the active component e.g., the active display
- the processor of the receiver 200 may again determine which active component and/or operation is consuming the most battery power and temporarily deactivate that particular component or operation.
- temperature damage to the battery may also be prevented using the power management module 300.
- a lithium-ion battery can be damaged if the battery is exposed to extreme temperatures, especially hot temperatures.
- low battery temperature may cause the internal resistance of the battery to increase significantly.
- the increase in internal resistance results in a voltage drop when the device turns on high current loads such as, for example, when a display of the receiver 200 is activated or when an alarm is output. It is beneficial to avoid or prevent voltage drops of a battery because a voltage drop may cause the operating system of the receiver 200 to unexpectedly reset. As a result of the reset, data may be lost.
- the temperature of the battery is monitored while the battery is being charged. If the temperature of the battery exceeds a threshold temperature, the processor of the receiver 200 issues a command to temporarily discontinue charging the battery.
- FIG. 4 illustrates a method 400 for determining whether a receiver, such as, for example receiver 200 (FIG. 2) is to enter a play dead mode, according to
- a processor of the receiver 200 determines an amount of power or charge remaining in a power source of the receiver 200 (410).
- a processor of the - - receiver 200 such as, for example, a user interface processor 310 (FIG. 3) is configured to collect and maintain battery information, such as charge count information (e.g., an amount of power remaining in the battery), at any given time.
- charge count information e.g., an amount of power remaining in the battery
- the user interface processor 310 of the receiver 200 may be configured to determine battery aging error. For example, due to the age of a battery, a small percentage of battery capacity may be lost during its usage.
- this error may be detected and the actual capacity of the battery based on the current age of the battery is updated.
- the determination is based on the current capacity of the aged battery rather than the capacity of the battery when it was new.
- the charge count of the battery is determined based on certain conditions. For example, if the receiver 200 is recovering from a hard or soft reset, battery information that was previously stored in a memory of the receiver 200 is checked to determine if the battery information is valid. Such a determination may be made by the processor comparing the stored battery information to an estimate of the remaining power in the power source. If the battery information stored in the memory is validated, the charge count of the battery is set as the battery information that is stored in the memory. In situations where the system is reset due to a power on procedure, such as for example, powering on the receiver 200, the charge count stored in the memory is retrieved and checked for validity.
- the stored battery information in memory is valid, the stored battery information is compared to an actual voltage reading from the battery. If the stored battery information is within a predetermined range, such as ⁇ 0.5 V of the actual voltage read from the battery, the charge count of the battery is set to the value that was stored in the memory. In another aspect, if it is determined by the user interface processor 330 that the battery voltage is below a minimum threshold, such as 3.6V or less, the charge count is set to zero and the receiver 200 enters play dead mode and/or prompts the user to begin recharging the battery. If the stored battery information is invalid, the charge count is initialized to zero and the user is prompted, via a display or alarm notification, that the battery of the receiver 200 needs to be recharged.
- a predetermined range such as ⁇ 0.5 V of the actual voltage read from the battery
- the charge count of the battery is set to the value that was stored in the memory. In another aspect, if it is determined by the user interface processor 330 that the battery voltage is below a minimum threshold, such as 3.6
- the user interface processor 330 of the receiver 200 receives a charge count interrupt signal, and based on the signal, determines when the battery is being charged, when the battery is fully charged, and when power from the battery is being discharged. For example, when the charge count interrupt signal is received by the processor and the signal is high, the user interface processor 330 is configured to increment a charge count. However, when the charge count interrupt signal is received and the signal is low, the user interface processor 330 subtracts one charge count. Thus, based on the charge count, the user interface processor 330 may determine how much power remains in the battery and/or when the charge count has reached a maximum count.
- the user interface processor 330 of the receiver 200 is configured to calculate and display an amount of power remaining in the battery of the receiver 200. As discussed above, when the remaining battery power reaches a predetermined minimum threshold level, the user interface processor 330 is configured to issue a command to output a notification to the user that the receiver 200 is about to enter the play dead mode because the remaining battery power is at or below a threshold power level. In another aspect, the user interface processor 330 is also configured to notify the user when the battery of the receiver 200 is fully charged. In certain embodiments, the display of the receiver 200 is configured to visually output the remaining power of the battery of the receiver 200.
- the remaining power of the battery of the receiver 200 is output in the form of an icon that displays an amount of power remaining in the battery. It also serves as an indication that all subsystems (e.g., test strip port functionality, display functionality, etc.) of the receiver 200 can be used without the risk of data loss or data corruption due to sudden or unexpected receiver 200 shutdown.
- all subsystems e.g., test strip port functionality, display functionality, etc.
- the battery icon is output on the display having at least four indicators with each of the indicators representing a portion of the battery life. Although four indicators are specifically mentioned, it is contemplated that any number of indicators may be used. As battery life of the receiver 200 drains, each of the indicators of the battery icon may be output in a different color. For example, as battery life is depleted from a 100% charge to a 75% charge, the user interface processor 330 of the receiver 200 causes the first indicator of the battery icon to change from green, to yellow to red to indicate that the user is reaching 75% charge while the remaining three indicators of the battery icon are output in green.
- the remaining three indicators are output in different colors to indicate the percentage of power - - remaining in the battery.
- the battery icon may also indicate the level or percentage of power remaining in the battery in which the user may continue to use all systems and functionalities of the receiver 200, such as, for example, the display or the test strip port 360. Additionally, the battery icon may display whether the battery of the receiver 200 is charging.
- the user interface processor 330 determines the amount of charge remaining in the battery of the receiver 200. If it is determined that the charge count of the battery is greater than the predetermined threshold, all subsystems and functionalities of the receiver remain active (450). However, if it is determined that the charge count of the battery is less than the predetermined threshold, the user interface processor 330 is configured to output a notification (430) that the receiver 200 will be entering the play dead mode and that some functionalities of the receiver 200 will be deactivated. In one aspect, the user interface processor 330 may be configured to determine which components of the receiver 200 are consuming the most power and selectively deactivate the identified components. Additionally, the notification may also indicate which components and/or operations of the receiver 200 will be deactivated when the play dead mode is entered.
- various alarms or other notifications may be output from the receiver 200 to warn the user that the power remaining in the battery is reaching a threshold level (e.g., 25% power).
- a threshold level e.g. 25% power
- multiple warnings or alerts may be output based on certain battery levels being reached. For example, when the amount of power remaining in the battery reaches a first level, a user is warned that the battery needs to be charged within a determined amount of time based on current battery power consumption. When the remaining amount of power in the battery reaches a second level, the receiver 200 enters the play dead mode (440).
- the user interface processor 330 of the receiver 200 is configured to estimate a time frame based on the current battery usage as to when the receiver 200 will enter the play dead mode. If the estimated amount of time elapses, the receiver 200 enters play dead mode (440).
- FIG. 5 is a state diagram of battery charge and discharge features of a receiver, such as, for example, receiver 200 (FIG. 2) according to embodiments of the present disclosure.
- various states of the battery include an initial state 500, a battery charging state 505, a charge complete 510 state, a discharging state 515, and play dead state 520. Although specific states have been discussed, it is understood that additional states may be used to govern the power supply.
- the battery remains in the charging state 505 when the receiver 200 is connected to a peripheral power source and the battery voltage and the receiver temperature are in a safe operation range.
- all operations and functionalities of the receiver 200 are operable except for test strip measurements and a user initiated self test of the receiver 200.
- a self test enables a user to select and run a self test mode in which the receiver 200 automatically tests whether various components of the receiver are working properly.
- Such components may include a display, a speaker, a memory, a vibratory indicator, and/or a test strip port light. After each successive test, the results may be audibly and/or visually output to a user.
- an icon may be output on the display to indicate that a battery of the receiver 200 is currently being charged.
- the receiver 200 enters the charge complete state 510 when the battery is completely charged and a USB cable is connected to the receiver 200.
- the processor such as, for example, the user interface processor 330 (FIG. 3) may be configured to cut off power to the battery so as not to overcharge the battery. As power from the battery is being discharged (e.g., 100% to 20% battery life remaining) all functionalities of the receiver 200 are active such as was described above with reference to FIG. 4.
- the display may be configured to graphically output the remaining battery power.
- the receiver 200 enters the play dead mode 520 described above. In the play dead mode 520, certain functionalities of the receiver 200 are inoperable. State transitions illustrated in FIG. 5 are further described in Table 2 below.
- the receiver 200 may be configured to enter play dead mode as a function of both voltage and temperature.
- An exemplary embodiment of the play dead mode is illustrated as the hatched region 600 of FIG. 6.
- the receiver 200 enters the play dead mode at different minimum voltages depending upon the battery temperature.
- the receiver 200 may be configured to enter the play dead mode when one of two temperatures and corresponding minimum voltages are reached.
- the two temperatures may be -5 0 C, and O 0 C, and the two corresponding minimum voltages may be 3.6V and 3.7V.
- the receiver 200 enters the play dead mode if the battery temperature is less than a first temperature (e.g., -5 0 C), regardless of the battery voltage.
- the receiver 200 enters the play dead mode if the battery temperature is between the first and second temperatures (e.g., 0 0 C and -5 0 C) and the battery voltage is less than a first battery voltage (e.g., about 3.7V). If the battery temperature is greater than the second temperature (e.g., O 0 C) or if the voltage is less than the second battery voltage (e.g., 3.7V), the receiver 200 will also enter the play dead mode.
- a first temperature e.g., -5 0 C
- the battery voltage e.g., about 3.7V
- battery temperature and voltage points may be selected, based upon the application (e.g., battery characteristics and power demands).
- the battery temperature and voltages that cause the transition to the play dead mode may be selectable and/or customizable by the user or health care professional.
- alarms are provided as illustrated by the solid and dashed lines 620, 630, 640.
- an alarm is output if the voltage of the battery is less than 3.75 V and the battery temperature is between O 0 C and -5 0 C (620).
- an alarm is output if the voltage is less than 3.65V and the battery temperature is greater than O 0 C (630).
- an alarm sounds if the battery temperature is less than 5 0 C and the voltage is greater than 3.6V (640).
- An auto-recover mode is identified by the dashed lines (650).
- the receiver 200 is configured automatically exit the play dead mode via the auto-recover mode when the processor detects that the voltage level of the battery exceeds 3.8 V and/or the battery temperature exceeds 8 0C.
- the receiver 200 may be configured to reduce the overall electronic noise of the receiver 200 during periods when data transmission is occurring, such as, for example, when the receiver 200 is expecting a data packet from a transmitter unit, such as, for example transmitter unit 102 (FIG. 1).
- a processor of the receiver 200 such as, for example, user interface processor 330 (FIG. 3) is configured to temporarily reduce the functionality of at least one component of the receiver 200 during the transmission of signals from the transmitter unit 102.
- One implementation of the noise reduction is referred to herein as the "quiet mode" in which the user interface processor 330 of the receiver 200 temporarily reduces the intensity of light from a display, such as an OLED display, of the receiver 200.
- the light level of the display is reduced for a short period of time which significantly reduces the noise caused by the display and improves RF performance.
- This reduction in light is virtually imperceptible to the user due to the very short duration of time in which the light has been reduced.
- the duration is about 15 to about 100 milliseconds and occurs once every 60 seconds or at time intervals that are determined based on, for example, expected time windows in which data packets are to be received from the transmitter unit 102.
- FIG. 7 another implementation of noise reduction is to effectively disconnect an antenna of an RF receiver 202 (FIG. 2) of the receiver 200 (FIG. 2) using an antenna switch.
- the signal generated by the sensor 101 is received from the transmitter 102 by an RF link, approximately once per minute.
- the RF reception signal path is from the antenna 710, through an antenna switch 720, into a transceiver 730.
- One purpose of the antenna switch 720 is to enable the antenna 710 to connect and disconnect to either the transmitter power amplifier or to the receiver 200.
- the antenna 710 is connected to the receiver 200 through the antenna switch 720 so as to enable the signal received from the transmitter unit 102 to be more accurate.
- a processor 740 e.g., glucose engine processor 350 (FIG. 3) of the receiver 200 controls the transceiver 730 and the antenna switch 720 in order to maximize noise reduction as will be described in greater detail below.
- control of the antenna switch 710 is provided by at least one processor of the receiver 200, such as, for example, the glucose engine processor 350 (FIG. 3) described above.
- This circuitry is represented as local interference sources 750 in the block diagram.
- the receiver 200 is sensitive to on channel signals at very low levels (e.g., about -110 dBm). However, this signal is desensitized by stronger signals such as, the local interference sources 750, even though the local interference sources 750 may not be on the same channel. As the local interference sources 750 are in close proximity to the antenna 710, the local interference sources 750 desensitize the RF receiver 202 and may corrupt the data received from the transmitter unit 102 or cause the data to be inaccurate.
- FIG. 8 illustrates a method 800 for reducing noise according to embodiments of the present disclosure.
- the method 800 described below may be used with components that were described above with respect to FIG. 7.
- the routine for reducing noise begins when the receiver, such as, for example, receiver 200 receives a sensor signal from the transmitter, such as, for example, transmitter unit 102 (810).
- the sensor signal is first received during the establishment of a transmission link between the receiver 200 and the transmitter 102 or the initial pairing of the receiver 200 and transmitter unit 102.
- a processor 740 (FIG. 7) of the receiver 200 activates a transceiver 730 and waits for the data packet to be transmitted from the transmitter unit 102.
- the data packet will arrive between 0 and 70 seconds after the transceiver 730 is activated. Although this range is specifically mentioned, it is contemplated that the data packet may arrive outside this time window, such as for example, after 70 seconds.
- the antenna switch 720 (FIG. 7) is used to effectively disconnect the antenna (820) from an RF receiver 202 (FIG. 2) of the receiver 200 which in turn reduces the effect of noise on the receiver 200. Because the RF receiver 202 is not using the antenna 710 the signal received from the transmitter unit 102 is attenuated by approximately 20 dB.
- the local noise level is also reduced by 20 dB which prevents the noise from substantially interfering and desensitizing the RF receiver 202 resulting in a more accurate signal.
- the receiver 200 may be in close proximity to the transmitter unit 102 such that the signal attenuation is acceptable. Disconnecting the antenna 710 during the initial pairing not only reduces noise, but also helps establish a communication range between the receiver 200 and the transmitter unit 210 when the antenna 710 is not used.
- the receiver 200 is configured to determine a window of time (830) in which the next data packet will arrive from the transmitter unit 102.
- the window of time is based on predetermined settings (e.g., once per minute).
- the - - window of time may be selected by a user or health care professional.
- the processor 740 activates the transceiver 730 for a short duration to receive the next data packet based on the determined window of time.
- a processor e.g., glucose engine processor 350 (FIG.
- the receiver 200 issues a command that causes one or more components (e.g., the local interference sources 750) of the receiver 200 to be deactivated (840) for a short period of time (e.g., 25 mS) without substantially affecting the other operations of the receiver 200.
- a command that causes one or more components (e.g., the local interference sources 750) of the receiver 200 to be deactivated (840) for a short period of time (e.g., 25 mS) without substantially affecting the other operations of the receiver 200.
- the processor 740 asserts a quite host signal 700 during the determined time window to indicate to the rest of the circuitry that it should enter a low power mode. Additionally, if it is determined that the receiver 200 is within range of the transmitter unit 102 such that the antenna 710 is not needed, the processor 740 issues a command to the switch 720 to disable the antenna (850) during the transmission time window. As a result, the noise level is further reduced.
- the range may be a predetermined range based on a strength of the signal being transmitted from the transmitter unit 102 to the receiver 200. In another embodiment, the range is established during the initial pairing of the receiver 200 and the transmitter unit 102 while the antenna 710 of the receiver 200 has been disconnected as was described above. Further description of implementing a quiet mode can be found in, among others, U.S. Patent Publication No.
- the quiet mode also refers to cessation of USB
- the quiet mode also refers to the design of quite mode blockers.
- the receiver 200 may have several different power modes. Such modes include power saving modes in which the power of external devices such as sound chips and LCD controllers are turned off. In such modes, the power consumption of one or more processors of the receiver is maintained at a minimum level.
- at least one processor, such as, for example the user interface processor 330 (FIG. 3) of the receiver 200 includes three modes to manage power consumption. In the first mode (e.g., a run mode), all - - components (e.g., a display, test strip port, flash memory, etc.) controlled by the user interface processor 330 are active. In this mode, power consumption is at a maximum rate. The second mode is a doze mode.
- At least one processor of the receiver 200 such as, for example the user interface processor 330 is essentially deactivated while a second processor, such as, for example the glucose engine processor 350, enables required peripherals to run (e.g., calibration modules, internal clocks etc.).
- a second processor such as, for example the glucose engine processor 350
- peripherals to run e.g., calibration modules, internal clocks etc.
- both of the processors of the receiver 200 are shut down and only a real time clock of the receiver 200 is active.
- FIG. 9 is a state diagram machine that illustrates the various states of power management of a receiver 200 such as were described above. These states include a "RUN MODE” state 910, in which at least one processor of the receiver, such as, for example a user interface processor 330 (FIG. 3) is in the run mode, referred to above. In the "STOP MODE” state 920, the user interface processor 330 of the receiver 200is in the stop mode as was described above. In the "QUIET MODE” state 930, the timers of the operating system of the receiver 200 and most interrupts are disabled, and one or more processors of the receiver 200 are placed into the stop mode as was described above.
- RUN MODE state 910
- STOP MODE the user interface processor 330 of the receiver 200is in the stop mode as was described above.
- the “QUIET MODE” state 930 the timers of the operating system of the receiver 200 and most interrupts are disabled, and one or more processors of the receiver 200 are placed into the stop mode as was described above.
- the receiver 200 to reach the power saving function, the receiver 200 must verify that there are no pending instructions that need to be executed prior to entering the power saving state. As such, blockers are used to indicate if a task or other executable action is in process and has not yet been completed. In certain embodiments, each blocker is a flag. If all the blockers are released (e.g., no flags are set), the receiver 200 enters the play dead mode such as was described above. In certain embodiment, the receiver uses the following exemplary blockers as set forth in Table 3 :
- the transitions between the states are illustrated and summarized in Table 4 below.
- the receiver 200 After power to the receiver 200 is turned on, the receiver 200 enters the RUN MODE state 910 (e.g., transition 905).
- the receiver 200 transitions from the RUN MODE state 910 to the STOP MODE state 920 (transition 915 ) when any of the blockers are not set and when a task is not scheduled to run.
- the STOP MODE state 920 at least one processor of the receiver 200 (e.g., the user interface processor 330) is deactivated and the receiver 200 enters the low power state.
- the receiver 200 is configured to transition from the
- STOP MODE state 920 to the RUN MODE state 910 under certain conditions.
- an interrupt signal can "wake up" the user interface processor 330 after the user interface processor 330 has entered the play dead mode such that the user interface processor returns to normal operation.
- a press of a button on the receiver 200, an OS timer, a USB cable plug-in and interrupt from the glucose engine processor 350 may wake up the deactivated user interface processor 330 so that receiver 200 runs in normal mode having all functionalities.
- the transition of the QUIET HOST signal to HIGH by the glucose engine processor 350, or the transition of the HOST A W AKE signal to HIGH will also transition the system from STOP MODE state 920 to the RUN MODE state 910.
- the phase locked loops of each processor e.g., the user interface processor 330 and the glucose engine processor 350
- clock 205 FIG. 2
- the - - receiver 200 enters the QUIET MODE state 930 from the RUN MODE state 910 when triggered by QUIET HOST signal such as described above with reference to FIGS. 7 and 8.
- the receiver 200 could transition to the QUIET MODE state 930 if and only if the glucose engine processor 350 raises the QUIET HOST signal (transition 935).
- the glucose engine processor 350 raises the QUIET HOST signal just prior to reception of the RF packet from the transmitter unit 102, for example, once every about 50-70 seconds. In some embodiments, transmission occurs once about every 60 seconds ⁇ 500 msec. Once the receiver 200 has entered the quite mode 930, this mode will persist for a predetermined amount of time (e.g., about 100 ms). When in the QUIET MODE state 930, the falling edge of the QUIET HOST transitions the receiver 200 out of the QUIET MODE state 930 to the RUN MODE state 910 (transition 940).
- additional considerations are provided prior to the receiver entering the quite mode. For example, if the system detects a USB connection when the system is in QUIET MODE state 930, there will be no USB interrupt because the USB is disabled in quite mode. If the user interface detects a QUIET HOST rising edge during uploading of data to a PC through the USB port, this request from glucose engine processor 350 to quiet the system will be ignored.
- noise reduction techniques are also employed by placement of the antenna in relation to the noise generating circuits.
- the antenna may be placed in an area so as to isolate the antenna from the noise source by being as far as physically possible from the noise source.
- noise sources may be placed as far as possible from the antenna. Additional design features may be included to increase the isolation, such a ground planes, metal shields, and slots cut in the printed circuit board.
- the antenna may be placed to improve signal strength by minimizing obstacles between the signal and antenna.
- considerations include hand placement positions when a user is holding the device as the user's hand may block the signal. Accordingly, the antenna may be placed on an outside edge that will not be covered by the hand of the user.
- an analyte monitoring device such as, for example a receiver, may be configured to enter an operating mode (e.g., a power conservation mode) in which certain functionalities and/or components of the analyte monitoring device are selectively disabled.
- this operating mode is entered when the remaining power of a power source of the analyte monitoring device has reached a predetermined minimum threshold level.
- the functionalities and/or components that are disabled are those components and/or functionalities that require the most battery power. Thus, disabling the components and/or functionalities that consume the most power may prolong the time before the analyte monitoring system shuts down due to lack of power which may result in the loss of data.
- Other conditions that may prompt the analyte monitoring device to enter the operating mode disclosed herein may include low or high operating temperatures of the analyte monitoring device that may cause data corruption or erroneous behavior if the analyte monitoring device were to continue operating under such conditions.
- a method is described in which one or more components of the analyte monitoring device are selectively deactivated during a time window in which the analyte monitoring device is to receive and/or transmit data. Because the one or more components are deactivated, the noise generated by those components is reduced which results in an enhanced and more accurate signal.
- Certain aspects of the present disclosure may include determining a temperature level of a power source of an analyte monitoring device, determining a level of power remaining in the power source of the analyte monitoring device, and selectively deactivating at least one component of the analyte monitoring device when at least one of the temperature level of the power source reaches a
- predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
- the at least one component may be a display.
- the display may be an organic light emitting diode (OLED) display.
- OLED organic light emitting diode
- the at least one component may be a test strip interface.
- the at least one component may be a memory device.
- the memory device may be a flash memory device.
- the predetermined temperature threshold may be about zero degrees Celsius.
- the predetermined temperature threshold may be about negative five degrees Celsius.
- the predetermined power threshold may be about 3.6V.
- the predetermined power threshold may be about 3.7V.
- selectively deactivating the at least one component may comprise determining an amount of power needed by the at least one component and deactivating the at least one component when the determined amount of power exceeds a threshold level.
- an apparatus may include one or more processors, and a memory operatively coupled to the one or more processors, the memory for storing instructions which, when executed by the one or more processors, causes the one or more processors to determine a temperature level of a power source of the apparatus, determine a level of power remaining in the power source of the apparatus, and selectively deactivate at least one component of the apparatus when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
- receiving unit comprising a radio frequency (RF) receiver, receiving a signal relating to an analyte concentration of a patient, determining a time window for receiving a subsequent signal corresponding to additional analyte concentrations of the patient, and selectively deactivating at least one of an antenna of the receiving unit or at least one component of the receiving unit during the determined time window.
- RF radio frequency
- the antenna may be deactivated using a switch.
- Certain embodiments may include determining a transmission range between the receiving unit and the transmitter.
- Certain embodiments may include deactivating the antenna when the
- determined transmission range is within a predetermined transmission range threshold.
- the transmission range may be based on a strength of the signal.
Abstract
Disclosed herein are methods and systems for conserving energy of a power source of an analyte monitoring device. Also disclosed herein are methods and systems for reducing noise during data transmissions to and from the analyte monitoring device.
Description
ANALYTE MONITORING SYSTEM AND METHODS FOR
MANAGING POWER AND NOISE
PRIORITY
[0001] The present application claims the benefit of U.S. Provisional Patent
Application No. 61/238,557, entitled "Analyte Monitoring System and Methods for Managing Power and Noise", filed on August 31, 2009, and U.S. Provisional Patent Application No. 61/247,537 entitled "Analyte Measurement System for Managing Hardware and Temperature", filed on September 30, 2009, the disclosures of each of which are incorporated herein by reference in their entirety for all purposes.
BACKGROUND
[0002] Diabetes Mellitus is an incurable chronic disease in which the body does not produce or properly utilize insulin. Insulin is a hormone produced by the pancreas that regulates blood sugar (glucose). In particular, when blood sugar levels rise, e.g., after a meal, insulin lowers the blood sugar levels by facilitating blood glucose to move from the blood into the body cells. Thus, when the pancreas does not produce sufficient insulin (a condition known as Type I Diabetes) or does not properly utilize insulin (a condition known as Type II Diabetes), the blood glucose remains in the blood resulting in hyperglycemia or abnormally high blood sugar levels.
[0003] The vast and uncontrolled fluctuations in blood glucose levels in people
suffering from diabetes cause long-term, serious complications. Some of these complications include blindness, kidney failure, and nerve damage. Additionally, it is known that diabetes is a factor in accelerating cardiovascular diseases such as atherosclerosis (hardening of the arteries), leading to stroke, coronary heart disease, and other diseases. Accordingly, one important and universal strategy in managing diabetes is to control blood glucose levels.
[0004] The first step in managing blood glucose levels is testing and monitoring blood glucose levels by using conventional techniques, such as drawing blood samples, applying the blood to a test strip, and determining the blood glucose level using colorimetric, electrochemical, or photometric test meters. Another more recent technique for monitoring blood glucose levels is by using a continuous or automatic glucose monitoring system. Unlike conventional blood glucose meters, continuous analyte monitoring systems employ an insertable or implantable sensor, which
- - continuously detects and monitors blood glucose levels. These blood glucose levels may then be displayed to a user to assist the user in managing the user's diabetes. However, as battery life drains from one or more components of the continuous analyte monitoring system, such as a receiver, data corresponding to the monitored blood glucose levels may be lost or become corrupt if the receiver of the analyte monitoring system shuts down due to lack of power in a rechargeable power source of the receiver. Additionally, noise produced by various components of the analyte monitoring system may interfere with a signal that conveys the monitored blood glucose levels.
INCORPORATED BY REFERENCE
[0005] The following patents, applications and/or publications are incorporated herein by reference for all purposes: U.S. Patent Nos. 4,545,382; 4,711,245; 5,262,035; 5,262,305; 5,264,104; 5,320,715; 5,356,786; 5,509,410; 5,543,326; 5,593,852; 5,601,435; 5,628,890; 5,820,551; 5,822,715; 5,899,855; 5,918,603; 6,071,391; 6,103,033; 6,120,676; 6,121,009; 6,134,461; 6,143,164; 6,144,837; 6,161,095; 6,175,752; 6,270,455; 6,284,478; 6,299,757; 6,338,790; 6,377,894; 6,461,496; 6,503,381; 6,514,460; 6,514,718; 6,540,891; 6,560,471; 6,579,690; 6,591,125; 6,592,745; 6,600,997; 6,605,200; 6,605,201; 6,616,819; 6,618,934; 6,650,471; 6,654,625; 6,676,816; 6,730,200; 6,736,957; 6,746,582; . 6,749,740; 6,764,581; 6,773,671; 6,881,551; 6,893,545; 6,932,892; 6,932,894; 6,942,518; 7,041,468; 7,167,818; and 7,299,082; U.S. Published Application Nos. 2004/0186365;
2005/0182306; 2006/0025662; 2006/0091006; 2007/0056858; 2007/0068807; 2007/0095661; 2007/0108048; 2007/0199818; 2007/0227911; 2007/0233013; 2008/0066305; 2008/0081977; 2008/0102441; 2008/0148873; 2008/0161666; 2008/0267823; and 2009/0054748; U.S. Patent Application Serial Nos. 11/461,725; 12/131,012; 12/393,921, 12/242,823; 12/363,712; 12/495,709; 12/698,124;
12/698,129; 12/714,439; 12/794,721; and 12/842,013, and U.S. Provisional Application Nos. 61/317,243, 61/345,562, and 61/361,374.
SUMMARY
[0006] Embodiments described herein relate to systems and methods for selectively disabling components of an analyte monitoring device based on a percentage of power remaining in a power source of the analyte monitoring device. As such, the
analyte monitoring device is configured to determine a temperature level of the power source of the analyte monitoring device, determine a level of power remaining in the power source of the analyte monitoring device, and selectively deactivate at least one component of the analyte monitoring device when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold. Also disclosed herein are methods and systems for reducing noise caused by components of the analyte monitoring device during data transmission and/or reception.
[0007] These and other objects, features and advantages of the present disclosure will become more fully apparent from the following detailed description of the embodiments, the appended claims and the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
[0008] A detailed description of various aspects, features, and embodiments of the subject matter described herein is provided with reference to the accompanying drawings, which are briefly described below. The drawings are illustrative and are not necessarily drawn to scale, with some components and features being exaggerated for clarity. The drawings illustrate various aspects and features of the present subject matter and may illustrate one or more embodiment(s) or example(s) of the present subject matter in whole or in part.
[0009] FIG. 1 illustrates a block diagram of a data monitoring and management system for according to embodiments of the present disclosure;
[0010] FIG. 2 is a block diagram of a receiver unit according to embodiments of the present disclosure;
[0011] FIG. 3 is a block diagram of a battery management feature of a receiver according to embodiments of the present disclosure;
[0012] FIG. 4 is a flow chart illustrating a method for determining whether a receiver is to enter a play dead mode according to embodiments of the present disclosure;
[0013] FIG. 5 is a state diagram of battery charge and discharge features of a receiver according to embodiments of the present disclosure;
[0014] FIG. 6 illustrates temperature and voltage conditions of a receiver entering a play dead mode according to embodiments of the present disclosure;
- -
[0015] FIG. 7 is a block diagram of a portion of a receiver according to embodiments of the present disclosure;
[0016] FIG. 8 is a flow chart illustrating a method for reducing noise according to embodiments of the present disclosure; and
[0017] FIG. 9 is a state diagram of a power mode of a receiver according to
embodiments of the present disclosure.
DETAILED DESCRIPTION
[0018] Before the present disclosure is described in detail, it is to be understood that this disclosure is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting, since the scope of the present disclosure will be limited only by the appended claims.
[0019] Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit unless the context clearly dictates otherwise, between the upper and lower limit of that range and any other stated or intervening value in that stated range, is encompassed within the disclosure. The upper and lower limits of these smaller ranges may independently be included in the smaller ranges is also encompassed within the disclosure, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either or both of those included limits are also included in the disclosure.
[0020] Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure belongs. Although any methods and materials similar or equivalent to those described herein can also be used in the practice or testing of the present disclosure, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited.
[0021] It must be noted that as used herein and in the appended claims, the singular forms "a", "an", and "the" include plural referents unless the context clearly dictates otherwise.
[0022] The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the present disclosure is not entitled to antedate such publication by virtue of prior disclosure. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.
[0023] As will be apparent to those of skill in the art upon reading this disclosure, each of the individual embodiments described and illustrated herein has discrete components and features which may be readily separated from or combined with the features of any of the other several embodiments without departing from the scope or spirit of the present disclosure.
[0024] The figures shown herein are not necessarily drawn to scale, with some
components and features being exaggerated for clarity.
[0025] Various exemplary embodiments of the analyte monitoring system and methods of the disclosure are described in further detail below. Although the disclosure is described primarily with respect to a glucose monitoring system, each aspect of the disclosure is not intended to be limited to the particular embodiment so described. Accordingly, it is to be understood that such description should not be construed to limit the scope of the disclosure, and it is to be understood that the analyte monitoring system can be configured to monitor a variety of analytes, as described below.
[0026] FIG. 1 illustrates a data monitoring and management system such as, for example, analyte (e.g., glucose) monitoring system 100 in accordance with embodiments of the present disclosure. In certain embodiments, the analyte monitoring system 100 may be a continuous monitoring system, a semi-continuous monitoring system, a discrete monitoring system or an on-demand monitoring system. The analyte monitoring system 100 includes a sensor 101, a transmitter unit 102 coupleable to the sensor 101, and a primary receiver unit 104 which is configured to communicate with the transmitter unit 102 via a bi-directional communication link 103. The primary receiver unit 104 may be further configured to transmit data to a data processing terminal 105 for evaluating the data received by the primary receiver unit 104. Moreover, the data processing terminal 105 in one embodiment may be configured to receive data directly from the transmitter unit 102 via a communication link which may optionally be configured for bi-directional
- - communication. Accordingly, transmitter unit 102 and/or receiver unit 104 may include a transceiver.
[0027] Also shown in FIG. 1 is an optional secondary receiver unit 106 which is operatively coupled to the communication link and configured to receive data transmitted from the transmitter unit 102. Moreover, as shown in the Figure, the secondary receiver unit 106 is configured to communicate with the primary receiver unit 104 as well as the data processing terminal 105. Indeed, the secondary receiver unit 106 may be configured for bidirectional wireless communication with each or one of the primary receiver unit 104 and the data processing terminal 105. In one embodiment of the present disclosure, the secondary receiver unit 106 may be configured to include a limited number of functions and features as compared with the primary receiver unit 104. As such, the secondary receiver unit 106 may be configured substantially in a smaller compact housing or embodied in a device such as a wrist watch, pager, mobile phone, Personal Digital Assistant (PDA), for example. Alternatively, the secondary receiver unit 106 may be configured with the same or substantially similar functionality as the primary receiver unit 104. The receiver unit may be configured to be used in conjunction with a docking cradle unit, for example for one or more of the following or other functions: placement by bedside, for re-charging, for data management, for night time monitoring, and/or bidirectional communication device.
[0028] In one aspect sensor 101 may include two or more sensors, each configured to communicate with transmitter unit 102. Furthermore, while only one, transmitter unit 102, communication link 103, and data processing terminal 105 are shown in the embodiment of the analyte monitoring system 100 illustrated in FIG. 1, in certain embodiments, the analyte monitoring system 100 may include one or more sensors, multiple transmitter units 102, communication links 103, and data processing terminals 105. Moreover, within the scope of the present disclosure, the analyte monitoring system 100 may be a continuous monitoring system, or semi- continuous, or a discrete monitoring system. In a multi-component environment, each device is configured to be uniquely identified by each of the other devices in the system so that communication conflict is readily resolved between the various components within the analyte monitoring system 100.
[0029] In one embodiment of the present disclosure, the sensor 101 is physically positioned in or on the body of a user whose analyte level is being monitored. The
sensor 101 may be configured to continuously sample the analyte level of the user and convert the sampled analyte level into a corresponding data signal for transmission by the transmitter unit 102. In certain embodiments, the transmitter unit 102 may be physically coupled to the sensor 101 so that both devices are integrated in a single housing and positioned on the user's body. The transmitter unit 102 may perform data processing such as filtering and encoding on data signals and/or other functions, each of which corresponds to a sampled analyte level of the user, and in any event transmitter unit 102 transmits analyte information to the primary receiver unit 104 via the communication link 103. Additional detailed description of the continuous analyte monitoring system, its various components including the functional descriptions of the transmitter are provided in but not limited to U.S. Patent Nos. 6,134,461, 6,175,752, 6,121,611, 6,560,471, and
6,746,582, and U.S. Patent Publication No. 2008/0278332 and elsewhere, the disclosures of each of which are incorporated by reference for all purposes.
30] FIG. 2 is a block diagram of a receiver 200 according to embodiments of the present disclosure. In certain embodiments, receiver 200 may be the primary receiver unit 104 (FIG. 1) or the secondary receiver unit 106 as described above. As illustrated in the block diagram, the receiver 200 includes an analyte test strip interface 201, (e.g., blood glucose test strip port), a radio frequency (RF) receiver 202, a user input mechanism 203 (e.g., one or more keys of a keypad, a touch- sensitive screen, a voice-activated input command unit etc.), a temperature detection section 204, and a clock 205, each of which is operatively coupled to a receiver processor 207. In certain embodiments, the receiver 200 also includes a power supply 206, such as, for example, a rechargeable battery, operatively coupled to a power conversion and monitoring section 208. Further, the power conversion and monitoring section are also coupled to the receiver processor 207. A receiver serial communication section 209, and an output 210, such as, for example a display, are each operatively coupled to the receiver processor 207. In certain embodiments and as briefly discussed above, the analyte monitoring system 100 is a continuous glucose monitoring system, and the test strip interface 201 includes a glucose level testing portion to manually receive a glucose test strip to determine the glucose level of a blood sample applied to the test strip. In response to receiving a test strip, the receiver 200 may be configured to output blood glucose information determined
from the test strip on the display. Additionally, the test strip can be used to calibrate a sensor such as, for example sensor 101.
[0031] In accordance with an embodiment, the receiver 200 includes two sections. The first section is an analog interface section that is configured to communicate with the transmitter unit 102 via the communication link 103. In certain embodiments, the analog interface section may include an RF receiver and an antenna for receiving and amplifying the data signals from the transmitter unit 102, which are thereafter, demodulated with a local oscillator and filtered through a band-pass filter. The second section of the receiver is a data processing section which is configured to process the data signals received from the transmitter unit 102 such as by performing data decoding, error detection and correction, data clock generation, and data bit recovery.
[0032] In certain embodiments, various data processing functionalities are executed by the receiver 200 such as, for example, calibration of analyte levels received from the sensor 101 and the transmitter unit 102 and techniques for managing power and noise of the analyte monitoring system 100, based on the periodic transmission of data from the transmitter unit 102.
[0033] In certain embodiments, a receiver 200 has an operating mode which prevents a user from operating the receiver 200 or suspends or deactivates certain
functionalities of the receiver during certain conditions. Such conditions may include a low battery level of the receiver 200, such as, for example, a low battery level that prompts hardware shutdown. Other conditions may include low or high operating temperatures of the receiver 200 that may cause data corruption or erroneous behavior if the receiver 200 were to continue operating under such conditions. As will be described in greater detail below, this suspended
functionality mode is referred herein as a play dead mode. In play dead mode, the receiver 200 continues to run a main clock and perform certain internal operations to keep desired data updated and current. Such operations and/or data may include operations and data corresponding to sensor life, calibration, timing of the receipt of data packets and the like. Although certain operations remain active, other operations of the receiver 200 are suspended. In certain embodiments, the operations that are suspended include writing data to memory, such as, for example a flash memory of the receiver 200, outputting sounds such as alarms, tones and/or
other notifications, displaying data on a display unit, or communicating commands to remotely controlled device, such as, for example, a pump.
[0034] In certain embodiments, one or more processors of the receiver 200 utilize a battery monitoring algorithm which performs a charge counting routine when determining whether to enter the play dead mode. More specifically, the charge counting routine in certain embodiments includes determining an estimate corresponding to an amount of battery charge available on a well-functioning battery during the lifecycle of the receiver 200. In certain embodiments, the battery monitoring algorithm takes into account variations in batteries from different manufacturers as well as an estimate of degradation of the battery capacity due to aging over the lifetime of the battery.
[0035] Referring to FIG. 3, in certain embodiments, the battery monitoring algorithm and associated battery management and charging functionalities of the receiver 200 is performed by power management module 300. In certain embodiments, the power management module 300 is equivalent to power conversion and monitoring section 208 (FIG. 2) and includes a battery charger 310 and a fuel gauge 320. In one aspect, the power management module 300 is configured to prevent a power supply 206 (e.g., rechargeable battery) of the receiver 200 from charging when a detected temperature of the receiver 200 and/or the battery is not in safe operating range. In certain embodiments, the power management module 300 is configured to prevent the battery from being continuously charged after the battery has been charging for a maximum charging period (e.g., more than about 3 hours). In certain embodiments, when the remaining power level of a battery of the receiver 200 reaches a predetermined minimum threshold level, the power management module 300 is configured to cut off power to one or more processors of the receiver 200, which may suspend or deactivate various functionalities of the receiver 200.
[0036] For example, the receiver 200 may have a user interface processor 330
configured to process commands received from, and output data to, various user interface components 340. In certain embodiments, the user interface components 340 may include, one or more buttons disposed on a housing of the receiver 200, a display, such as, for example a touch sensitive display, a sound synthesizer, a vibration component, and/or a backlight. Although specific components are mentioned, it is contemplated that the receiver may include additional user interface components configured to enable a user to interact with the receiver 200. In certain
embodiments, the user interface processor 330 is configured to interact with the various user interface components 340 including updating the display of the receiver 200, processing received glucose data, maintaining a log of historical information, operating the sound synthesizer and/or the vibration component, and/or interface with the power management module 300. In addition to the user interface processor 330, the receiver 200 may also include glucose engine processor 350 configured to receive and process analyte data received from a transmitter, such as, for example, transmitter unit 102 (FIG. 1) and/or data received from a test strip port 360. In certain embodiments, test strip port 360 may be equivalent to test strip interface 201 (FIG. 2). Depending on how much power each of the above mentioned processors are consuming, one or more operations or functionalities of the receiver 200 that are controlled by each of the above mentioned processors may be deactivated or suspended when entering the play dead mode.
[0037] In certain embodiments, the battery monitoring algorithm discussed above incorporates several design constraints and considerations. For example, one consideration is discharge of the battery of the receiver 200. In one aspect, the battery of the receiver 200 is a lithium-ion battery. As these types of batteries may be damaged when deeply discharged (e.g., discharging the battery below a certain percentage of the charge capacity of the battery), the power management module 300 may be configured to cut or reduce power to one or more processors of the receiver 200 when the battery voltage drops below a certain voltage minimum threshold (e.g., about 3.3V).
[0038] In certain embodiments, when the voltage remaining in the battery drops below a certain threshold, for example about 3.6V, the battery is considered an empty battery and the power management module 300 reduces or cuts power to one or more of the processors to conserve the remaining battery power. In such situations, and as described above, when the power management module 300 cuts power from the battery, certain functionalities of the receiver 200 are disabled while other functionalities of the receiver 200 may remain active. In one aspect, one or more processors of the receiver 200 may be configured to determine which components and/or operations (e.g. writing to flash memory, updating a display, etc.) controlled by a particular processor are consuming the most power. The processor may then deactivate one or more operations and/or components that are consuming the most
power while other operations and/or components controlled by that processor remain active.
[0039] For example, the user interface processor 330 may control a display and a light source of the receiver 200. When battery power reaches the predetermined minimum threshold, the user interface processor 350 may determine that continued operation of the light source will require more power than operation of the display. As such, the light source will be deactivated until the battery of the receiver 200 is recharged, but the display remains active. Although one component controlled by a processor may remain active while another component is deactivated as was described above, it is contemplated that as battery power continues to drain, the active component (e.g., the active display) controlled by the user interface processor 330 may be subsequently deactivated when remaining power of the battery reaches a second predetermined minimum threshold. When this threshold is reached, the processor of the receiver 200 may again determine which active component and/or operation is consuming the most battery power and temporarily deactivate that particular component or operation.
[0040] In another aspect, temperature damage to the battery may also be prevented using the power management module 300. For example, a lithium-ion battery can be damaged if the battery is exposed to extreme temperatures, especially hot temperatures. Additionally, low battery temperature may cause the internal resistance of the battery to increase significantly. The increase in internal resistance results in a voltage drop when the device turns on high current loads such as, for example, when a display of the receiver 200 is activated or when an alarm is output. It is beneficial to avoid or prevent voltage drops of a battery because a voltage drop may cause the operating system of the receiver 200 to unexpectedly reset. As a result of the reset, data may be lost. In certain embodiments, the temperature of the battery is monitored while the battery is being charged. If the temperature of the battery exceeds a threshold temperature, the processor of the receiver 200 issues a command to temporarily discontinue charging the battery.
[0041] FIG. 4 illustrates a method 400 for determining whether a receiver, such as, for example receiver 200 (FIG. 2) is to enter a play dead mode, according to
embodiments of the present disclosure. Referring to FIG. 4, initially a processor of the receiver 200 determines an amount of power or charge remaining in a power source of the receiver 200 (410). In certain embodiments, a processor of the
- - receiver 200, such as, for example, a user interface processor 310 (FIG. 3), is configured to collect and maintain battery information, such as charge count information (e.g., an amount of power remaining in the battery), at any given time. In addition to determining the battery information, the user interface processor 310 of the receiver 200 may be configured to determine battery aging error. For example, due to the age of a battery, a small percentage of battery capacity may be lost during its usage. Accordingly, this error may be detected and the actual capacity of the battery based on the current age of the battery is updated. Thus, when the remaining charge level of the battery is determined, the determination is based on the current capacity of the aged battery rather than the capacity of the battery when it was new.
[0042] In certain embodiments, when the receiver 200 is powered on, the charge count of the battery is determined based on certain conditions. For example, if the receiver 200 is recovering from a hard or soft reset, battery information that was previously stored in a memory of the receiver 200 is checked to determine if the battery information is valid. Such a determination may be made by the processor comparing the stored battery information to an estimate of the remaining power in the power source. If the battery information stored in the memory is validated, the charge count of the battery is set as the battery information that is stored in the memory. In situations where the system is reset due to a power on procedure, such as for example, powering on the receiver 200, the charge count stored in the memory is retrieved and checked for validity. If the battery information in memory is valid, the stored battery information is compared to an actual voltage reading from the battery. If the stored battery information is within a predetermined range, such as ±0.5 V of the actual voltage read from the battery, the charge count of the battery is set to the value that was stored in the memory. In another aspect, if it is determined by the user interface processor 330 that the battery voltage is below a minimum threshold, such as 3.6V or less, the charge count is set to zero and the receiver 200 enters play dead mode and/or prompts the user to begin recharging the battery. If the stored battery information is invalid, the charge count is initialized to zero and the user is prompted, via a display or alarm notification, that the battery of the receiver 200 needs to be recharged.
[0043] In certain embodiments, the user interface processor 330 of the receiver 200 receives a charge count interrupt signal, and based on the signal, determines when
the battery is being charged, when the battery is fully charged, and when power from the battery is being discharged. For example, when the charge count interrupt signal is received by the processor and the signal is high, the user interface processor 330 is configured to increment a charge count. However, when the charge count interrupt signal is received and the signal is low, the user interface processor 330 subtracts one charge count. Thus, based on the charge count, the user interface processor 330 may determine how much power remains in the battery and/or when the charge count has reached a maximum count.
[0044] In certain embodiments, the user interface processor 330 of the receiver 200 is configured to calculate and display an amount of power remaining in the battery of the receiver 200. As discussed above, when the remaining battery power reaches a predetermined minimum threshold level, the user interface processor 330 is configured to issue a command to output a notification to the user that the receiver 200 is about to enter the play dead mode because the remaining battery power is at or below a threshold power level. In another aspect, the user interface processor 330 is also configured to notify the user when the battery of the receiver 200 is fully charged. In certain embodiments, the display of the receiver 200 is configured to visually output the remaining power of the battery of the receiver 200. In certain embodiments, the remaining power of the battery of the receiver 200 is output in the form of an icon that displays an amount of power remaining in the battery. It also serves as an indication that all subsystems (e.g., test strip port functionality, display functionality, etc.) of the receiver 200 can be used without the risk of data loss or data corruption due to sudden or unexpected receiver 200 shutdown.
[0045] In certain embodiments, the battery icon is output on the display having at least four indicators with each of the indicators representing a portion of the battery life. Although four indicators are specifically mentioned, it is contemplated that any number of indicators may be used. As battery life of the receiver 200 drains, each of the indicators of the battery icon may be output in a different color. For example, as battery life is depleted from a 100% charge to a 75% charge, the user interface processor 330 of the receiver 200 causes the first indicator of the battery icon to change from green, to yellow to red to indicate that the user is reaching 75% charge while the remaining three indicators of the battery icon are output in green. As power of the battery of the receiver 200 is continually discharged, the remaining three indicators are output in different colors to indicate the percentage of power
- - remaining in the battery. In certain embodiments, the battery icon may also indicate the level or percentage of power remaining in the battery in which the user may continue to use all systems and functionalities of the receiver 200, such as, for example, the display or the test strip port 360. Additionally, the battery icon may display whether the battery of the receiver 200 is charging.
[0046] Referring back to FIG. 4, once the user interface processor 330 has determined the amount of charge remaining in the battery of the receiver 200, the determined amount of charge is compared to a minimum predetermined power threshold level (420). If it is determined that the charge count of the battery is greater than the predetermined threshold, all subsystems and functionalities of the receiver remain active (450). However, if it is determined that the charge count of the battery is less than the predetermined threshold, the user interface processor 330 is configured to output a notification (430) that the receiver 200 will be entering the play dead mode and that some functionalities of the receiver 200 will be deactivated. In one aspect, the user interface processor 330 may be configured to determine which components of the receiver 200 are consuming the most power and selectively deactivate the identified components. Additionally, the notification may also indicate which components and/or operations of the receiver 200 will be deactivated when the play dead mode is entered.
[0047] In certain embodiments, various alarms or other notifications may be output from the receiver 200 to warn the user that the power remaining in the battery is reaching a threshold level (e.g., 25% power). In another embodiment, multiple warnings or alerts may be output based on certain battery levels being reached. For example, when the amount of power remaining in the battery reaches a first level, a user is warned that the battery needs to be charged within a determined amount of time based on current battery power consumption. When the remaining amount of power in the battery reaches a second level, the receiver 200 enters the play dead mode (440). In another embodiment, the user interface processor 330 of the receiver 200 is configured to estimate a time frame based on the current battery usage as to when the receiver 200 will enter the play dead mode. If the estimated amount of time elapses, the receiver 200 enters play dead mode (440).
[0048] Additional description of alarms and the output of the alarms and play dead mode for certain embodiments are shown in Table 1 below.
- - TABLE 1
[0049] FIG. 5 is a state diagram of battery charge and discharge features of a receiver, such as, for example, receiver 200 (FIG. 2) according to embodiments of the present disclosure. As shown in FIG. 5, various states of the battery include an initial state 500, a battery charging state 505, a charge complete 510 state, a discharging state 515, and play dead state 520. Although specific states have been discussed, it is understood that additional states may be used to govern the power supply.
[0050] In certain embodiments, the battery remains in the charging state 505 when the receiver 200 is connected to a peripheral power source and the battery voltage and the receiver temperature are in a safe operation range. In the charging state 505, all operations and functionalities of the receiver 200 are operable except for test strip measurements and a user initiated self test of the receiver 200. In certain embodiments, a self test enables a user to select and run a self test mode in which the receiver 200 automatically tests whether various components of the receiver are working properly. Such components may include a display, a speaker, a memory, a vibratory indicator, and/or a test strip port light. After each successive test, the results may be audibly and/or visually output to a user. Although specific self tests have been mentioned, it is contemplated that additional self tests related to other components of the receiver may be performed.
- -
[0051] As discussed above, when in the charging state 505, an icon may be output on the display to indicate that a battery of the receiver 200 is currently being charged. In one aspect, the receiver 200 enters the charge complete state 510 when the battery is completely charged and a USB cable is connected to the receiver 200. However, as stated above, although the receiver 200 may still be connected to a power source, when the fully charged state 510 is reached, the processor, such as, for example, the user interface processor 330 (FIG. 3) may be configured to cut off power to the battery so as not to overcharge the battery. As power from the battery is being discharged (e.g., 100% to 20% battery life remaining) all functionalities of the receiver 200 are active such as was described above with reference to FIG. 4.
Additionally, the display may be configured to graphically output the remaining battery power.
[0052] When battery life reaches about 20% to 0%, the receiver 200 enters the play dead mode 520 described above. In the play dead mode 520, certain functionalities of the receiver 200 are inoperable. State transitions illustrated in FIG. 5 are further described in Table 2 below.
- - TABLE 2
53] Further aspects of the play dead mode are illustrated in FIG. 6. For example, in certain embodiments, the receiver 200 (FIG. 2) may be configured to enter play dead mode as a function of both voltage and temperature. An exemplary embodiment of the play dead mode is illustrated as the hatched region 600 of FIG. 6. For example, the receiver 200 enters the play dead mode at different minimum voltages depending upon the battery temperature. In one aspect, the receiver 200 may be configured to enter the play dead mode when one of two temperatures and corresponding minimum voltages are reached. For example, the two temperatures may be -50C, and O0C, and the two corresponding minimum voltages may be 3.6V and 3.7V. As
indicated by solid black line 610, the receiver 200 enters the play dead mode if the battery temperature is less than a first temperature (e.g., -50C), regardless of the battery voltage. In another embodiment, the receiver 200 enters the play dead mode if the battery temperature is between the first and second temperatures (e.g., 0 0C and -50C) and the battery voltage is less than a first battery voltage (e.g., about 3.7V). If the battery temperature is greater than the second temperature (e.g., O0C) or if the voltage is less than the second battery voltage (e.g., 3.7V), the receiver 200 will also enter the play dead mode. It is understood that a fewer or greater number of battery temperature and voltage points may be selected, based upon the application (e.g., battery characteristics and power demands). Moreover, the battery temperature and voltages that cause the transition to the play dead mode may be selectable and/or customizable by the user or health care professional.
[0054] With continued reference to FIG. 6, alarms are provided as illustrated by the solid and dashed lines 620, 630, 640. As indicated by arrow 1, an alarm is output if the voltage of the battery is less than 3.75 V and the battery temperature is between O0C and -50C (620). As indicated by arrow 2, an alarm is output if the voltage is less than 3.65V and the battery temperature is greater than O0C (630). As indicated by arrow 3, an alarm sounds if the battery temperature is less than 50C and the voltage is greater than 3.6V (640). An auto-recover mode is identified by the dashed lines (650). In certain embodiments, the receiver 200 is configured automatically exit the play dead mode via the auto-recover mode when the processor detects that the voltage level of the battery exceeds 3.8 V and/or the battery temperature exceeds 8 0C.
[0055] In another aspect of the present disclosure, the receiver 200 may be configured to reduce the overall electronic noise of the receiver 200 during periods when data transmission is occurring, such as, for example, when the receiver 200 is expecting a data packet from a transmitter unit, such as, for example transmitter unit 102 (FIG. 1). To accomplish the noise reduction, a processor of the receiver 200, such as, for example, user interface processor 330 (FIG. 3) is configured to temporarily reduce the functionality of at least one component of the receiver 200 during the transmission of signals from the transmitter unit 102.
[0056] One implementation of the noise reduction is referred to herein as the "quiet mode" in which the user interface processor 330 of the receiver 200 temporarily reduces the intensity of light from a display, such as an OLED display, of the
receiver 200. During the RF packet reception, the light level of the display is reduced for a short period of time which significantly reduces the noise caused by the display and improves RF performance. This reduction in light is virtually imperceptible to the user due to the very short duration of time in which the light has been reduced. In some embodiments, the duration is about 15 to about 100 milliseconds and occurs once every 60 seconds or at time intervals that are determined based on, for example, expected time windows in which data packets are to be received from the transmitter unit 102.
[0057] Referring to FIG. 7, another implementation of noise reduction is to effectively disconnect an antenna of an RF receiver 202 (FIG. 2) of the receiver 200 (FIG. 2) using an antenna switch. As discussed herein, the signal generated by the sensor 101 is received from the transmitter 102 by an RF link, approximately once per minute. The RF reception signal path is from the antenna 710, through an antenna switch 720, into a transceiver 730. One purpose of the antenna switch 720 is to enable the antenna 710 to connect and disconnect to either the transmitter power amplifier or to the receiver 200. In certain embodiments, the antenna 710 is connected to the receiver 200 through the antenna switch 720 so as to enable the signal received from the transmitter unit 102 to be more accurate. A processor 740 (e.g., glucose engine processor 350 (FIG. 3)) of the receiver 200 controls the transceiver 730 and the antenna switch 720 in order to maximize noise reduction as will be described in greater detail below.
[0058] In certain embodiments, control of the antenna switch 710 is provided by at least one processor of the receiver 200, such as, for example, the glucose engine processor 350 (FIG. 3) described above. Other circuits on the receiver 200 that perform functions unrelated to data reception from the transmitter unit 102, such as, for example, the user interface processor 330, can generate RF noise that interferes with the signal. This circuitry is represented as local interference sources 750 in the block diagram.
[0059] In certain embodiments, the receiver 200 is sensitive to on channel signals at very low levels (e.g., about -110 dBm). However, this signal is desensitized by stronger signals such as, the local interference sources 750, even though the local interference sources 750 may not be on the same channel. As the local interference sources 750 are in close proximity to the antenna 710, the local interference sources
750 desensitize the RF receiver 202 and may corrupt the data received from the transmitter unit 102 or cause the data to be inaccurate.
[0060] FIG. 8 illustrates a method 800 for reducing noise according to embodiments of the present disclosure. Referring to FIG. 8, in certain embodiments, the method 800 described below may be used with components that were described above with respect to FIG. 7. The routine for reducing noise begins when the receiver, such as, for example, receiver 200 receives a sensor signal from the transmitter, such as, for example, transmitter unit 102 (810). In certain embodiments, the sensor signal is first received during the establishment of a transmission link between the receiver 200 and the transmitter 102 or the initial pairing of the receiver 200 and transmitter unit 102. When establishing the transmission link, a processor 740 (FIG. 7) of the receiver 200 activates a transceiver 730 and waits for the data packet to be transmitted from the transmitter unit 102. Typically, the data packet will arrive between 0 and 70 seconds after the transceiver 730 is activated. Although this range is specifically mentioned, it is contemplated that the data packet may arrive outside this time window, such as for example, after 70 seconds. In order to reduce the affects of local interference sources, the antenna switch 720 (FIG. 7) is used to effectively disconnect the antenna (820) from an RF receiver 202 (FIG. 2) of the receiver 200 which in turn reduces the effect of noise on the receiver 200. Because the RF receiver 202 is not using the antenna 710 the signal received from the transmitter unit 102 is attenuated by approximately 20 dB. Although the signal is attenuated by 20 dB, the local noise level is also reduced by 20 dB which prevents the noise from substantially interfering and desensitizing the RF receiver 202 resulting in a more accurate signal. Further , even though the signal is attenuated by 20 dB, the receiver 200 may be in close proximity to the transmitter unit 102 such that the signal attenuation is acceptable. Disconnecting the antenna 710 during the initial pairing not only reduces noise, but also helps establish a communication range between the receiver 200 and the transmitter unit 210 when the antenna 710 is not used.
[0061] Once the receiver 200 has received the first data packet and established a range of communication without the antenna 710 being used, the receiver 200 is configured to determine a window of time (830) in which the next data packet will arrive from the transmitter unit 102. In certain embodiments, the window of time is based on predetermined settings (e.g., once per minute). In another embodiment, the
- - window of time may be selected by a user or health care professional. Once the time window is determined, the processor 740 activates the transceiver 730 for a short duration to receive the next data packet based on the determined window of time. During the determined window of time, a processor (e.g., glucose engine processor 350 (FIG. 3)) of the receiver 200 issues a command that causes one or more components (e.g., the local interference sources 750) of the receiver 200 to be deactivated (840) for a short period of time (e.g., 25 mS) without substantially affecting the other operations of the receiver 200.
[0062] In certain embodiments, the processor 740 asserts a quite host signal 700 during the determined time window to indicate to the rest of the circuitry that it should enter a low power mode. Additionally, if it is determined that the receiver 200 is within range of the transmitter unit 102 such that the antenna 710 is not needed, the processor 740 issues a command to the switch 720 to disable the antenna (850) during the transmission time window. As a result, the noise level is further reduced. In certain embodiments, the range may be a predetermined range based on a strength of the signal being transmitted from the transmitter unit 102 to the receiver 200. In another embodiment, the range is established during the initial pairing of the receiver 200 and the transmitter unit 102 while the antenna 710 of the receiver 200 has been disconnected as was described above. Further description of implementing a quiet mode can be found in, among others, U.S. Patent Publication No.
2009/0076359, the disclosure of which is incorporated herein by reference for all purposes.
[0063] In certain embodiments, the quiet mode also refers to cessation of USB
communication such as, for example, communication between the receiver 200 and peripheral device, such as, for example, a remoter computer. In one aspect, as will be described in detail below, the quiet mode also refers to the design of quite mode blockers.
[0064] In certain embodiments, the receiver 200 may have several different power modes. Such modes include power saving modes in which the power of external devices such as sound chips and LCD controllers are turned off. In such modes, the power consumption of one or more processors of the receiver is maintained at a minimum level. In certain embodiments, at least one processor, such as, for example the user interface processor 330 (FIG. 3) of the receiver 200 includes three modes to manage power consumption. In the first mode (e.g., a run mode), all
- - components (e.g., a display, test strip port, flash memory, etc.) controlled by the user interface processor 330 are active. In this mode, power consumption is at a maximum rate. The second mode is a doze mode. In the doze mode, at least one processor of the receiver 200, such as, for example the user interface processor 330 is essentially deactivated while a second processor, such as, for example the glucose engine processor 350, enables required peripherals to run (e.g., calibration modules, internal clocks etc.). In the stop mode, both of the processors of the receiver 200 are shut down and only a real time clock of the receiver 200 is active.
[0065] FIG. 9 is a state diagram machine that illustrates the various states of power management of a receiver 200 such as were described above. These states include a "RUN MODE" state 910, in which at least one processor of the receiver, such as, for example a user interface processor 330 (FIG. 3) is in the run mode, referred to above. In the "STOP MODE" state 920, the user interface processor 330 of the receiver 200is in the stop mode as was described above. In the "QUIET MODE" state 930, the timers of the operating system of the receiver 200 and most interrupts are disabled, and one or more processors of the receiver 200 are placed into the stop mode as was described above.
[0066] In certain embodiments, to reach the power saving function, the receiver 200 must verify that there are no pending instructions that need to be executed prior to entering the power saving state. As such, blockers are used to indicate if a task or other executable action is in process and has not yet been completed. In certain embodiments, each blocker is a flag. If all the blockers are released (e.g., no flags are set), the receiver 200 enters the play dead mode such as was described above. In certain embodiment, the receiver uses the following exemplary blockers as set forth in Table 3 :
- - TABLE 3
67] Referring back to FIG. 9, the transitions between the states, in certain embodiments, are illustrated and summarized in Table 4 below. After power to the receiver 200 is turned on, the receiver 200 enters the RUN MODE state 910 (e.g., transition 905). The receiver 200 transitions from the RUN MODE state 910 to the STOP MODE state 920 (transition 915 ) when any of the blockers are not set and when a task is not scheduled to run. In entering the STOP MODE state 920, at least one processor of the receiver 200 (e.g., the user interface processor 330) is deactivated and the receiver 200 enters the low power state.
- - TABLE 4
[0068] In one aspect, the receiver 200 is configured to transition from the
STOP MODE state 920 to the RUN MODE state 910 (transition 925) under certain conditions. For example, an interrupt signal can "wake up" the user interface processor 330 after the user interface processor 330 has entered the play dead mode such that the user interface processor returns to normal operation. In certain embodiments, a press of a button on the receiver 200, an OS timer, a USB cable plug-in and interrupt from the glucose engine processor 350 may wake up the deactivated user interface processor 330 so that receiver 200 runs in normal mode having all functionalities. In addition, the transition of the QUIET HOST signal to HIGH by the glucose engine processor 350, or the transition of the HOST A W AKE signal to HIGH will also transition the system from STOP MODE state 920 to the RUN MODE state 910.
[0069] Referring to the quiet mode 930, when in the quiet mode 930, the phase locked loops of each processor (e.g., the user interface processor 330 and the glucose engine processor 350) are shut down and clock 205 (FIG. 2) is stopped. The
- - receiver 200 enters the QUIET MODE state 930 from the RUN MODE state 910 when triggered by QUIET HOST signal such as described above with reference to FIGS. 7 and 8. For example, the receiver 200 could transition to the QUIET MODE state 930 if and only if the glucose engine processor 350 raises the QUIET HOST signal (transition 935). The glucose engine processor 350 raises the QUIET HOST signal just prior to reception of the RF packet from the transmitter unit 102, for example, once every about 50-70 seconds. In some embodiments, transmission occurs once about every 60 seconds ±500 msec. Once the receiver 200 has entered the quite mode 930, this mode will persist for a predetermined amount of time (e.g., about 100 ms). When in the QUIET MODE state 930, the falling edge of the QUIET HOST transitions the receiver 200 out of the QUIET MODE state 930 to the RUN MODE state 910 (transition 940).
[0070] In certain embodiments, additional considerations are provided prior to the receiver entering the quite mode. For example, if the system detects a USB connection when the system is in QUIET MODE state 930, there will be no USB interrupt because the USB is disabled in quite mode. If the user interface detects a QUIET HOST rising edge during uploading of data to a PC through the USB port, this request from glucose engine processor 350 to quiet the system will be ignored.
[0071] There are occasions that continuous communications between the receiver 200 and an external device (e.g., a remote computer) are required for an extended period (e.g., for debugging, product engineering, hardware verification and validation, historical data upload, etc). During such extended communications, it may be desirable to block the quite mode entirely. Once the quiet mode is deactivated, communication between the remoter computer and the receiver may occur. In certain embodiments, the communication link between the remote computer and receiver only occurs when data packets are not being received by the receiver. At the end of the period of time between packets, the PC application closes the communication link and waits for a signal which indicates that the packet transmission has been completed. In some embodiments, this process will continue as long as the PC application wants to communicate to device. This technique may avoid the dangling and hanging of the PC application as a result of the receiver going to the quiet mode and shutting down the USB clock before the PC application closes the USB port.
- -
[0072] In yet another embodiment, noise reduction techniques are also employed by placement of the antenna in relation to the noise generating circuits. In such embodiments, the antenna may be placed in an area so as to isolate the antenna from the noise source by being as far as physically possible from the noise source.
Conversely, it is also contemplated that noise sources may be placed as far as possible from the antenna. Additional design features may be included to increase the isolation, such a ground planes, metal shields, and slots cut in the printed circuit board.
[0073] Additionally, it is contemplated that the antenna may be placed to improve signal strength by minimizing obstacles between the signal and antenna. Such considerations include hand placement positions when a user is holding the device as the user's hand may block the signal. Accordingly, the antenna may be placed on an outside edge that will not be covered by the hand of the user.
[0074] In the manner described above, an analyte monitoring device, such as, for example a receiver, may be configured to enter an operating mode (e.g., a power conservation mode) in which certain functionalities and/or components of the analyte monitoring device are selectively disabled. In certain embodiments, this operating mode is entered when the remaining power of a power source of the analyte monitoring device has reached a predetermined minimum threshold level. In certain embodiments, the functionalities and/or components that are disabled are those components and/or functionalities that require the most battery power. Thus, disabling the components and/or functionalities that consume the most power may prolong the time before the analyte monitoring system shuts down due to lack of power which may result in the loss of data. Other conditions that may prompt the analyte monitoring device to enter the operating mode disclosed herein may include low or high operating temperatures of the analyte monitoring device that may cause data corruption or erroneous behavior if the analyte monitoring device were to continue operating under such conditions.
[0075] In certain embodiments of the present disclosure, a method is described in which one or more components of the analyte monitoring device are selectively deactivated during a time window in which the analyte monitoring device is to receive and/or transmit data. Because the one or more components are deactivated, the noise generated by those components is reduced which results in an enhanced and more accurate signal.
- -
[0076] Certain aspects of the present disclosure may include determining a temperature level of a power source of an analyte monitoring device, determining a level of power remaining in the power source of the analyte monitoring device, and selectively deactivating at least one component of the analyte monitoring device when at least one of the temperature level of the power source reaches a
predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
[0077] In certain embodiments, the at least one component may be a display.
[0078] In certain embodiments, the display may be an organic light emitting diode (OLED) display.
[0079] In certain embodiments, the at least one component may be a test strip interface.
[0080] In certain embodiments, the at least one component may be a memory device.
[0081] In certain embodiments, the memory device may be a flash memory device.
[0082] In certain embodiments, the predetermined temperature threshold may be about zero degrees Celsius.
[0083] In certain embodiments, the predetermined temperature threshold may be about negative five degrees Celsius.
[0084] In certain embodiments, the predetermined power threshold may be about 3.6V.
[0085] In certain embodiments, the predetermined power threshold may be about 3.7V.
[0086] In certain embodiments, selectively deactivating the at least one component may comprise determining an amount of power needed by the at least one component and deactivating the at least one component when the determined amount of power exceeds a threshold level.
[0087] In other certain aspects of the present disclosure, an apparatus may include one or more processors, and a memory operatively coupled to the one or more processors, the memory for storing instructions which, when executed by the one or more processors, causes the one or more processors to determine a temperature level of a power source of the apparatus, determine a level of power remaining in the power source of the apparatus, and selectively deactivate at least one component of the apparatus when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
[0088] Other certain aspects of the present disclosure may include providing a
receiving unit comprising a radio frequency (RF) receiver, receiving a signal relating
to an analyte concentration of a patient, determining a time window for receiving a subsequent signal corresponding to additional analyte concentrations of the patient, and selectively deactivating at least one of an antenna of the receiving unit or at least one component of the receiving unit during the determined time window.
[0089] In certain embodiments, the antenna may be deactivated using a switch.
[0090] Certain embodiments may include determining a transmission range between the receiving unit and the transmitter.
[0091] Certain embodiments may include deactivating the antenna when the
determined transmission range is within a predetermined transmission range threshold.
[0092] In certain embodiments, the transmission range may be based on a strength of the signal.
[0093] Various other modifications and alterations in the structure and method of operation of this disclosure will be apparent to those skilled in the art without departing from the scope and spirit of the embodiments of the present disclosure. Although the present disclosure has been described in connection with particular embodiments, it should be understood that the present disclosure as claimed should not be unduly limited to such particular embodiments. It is intended that the following claims define the scope of the present disclosure and that structures and methods within the scope of these claims and their equivalents be covered thereby.
Claims
1. A method comprising:
determining a temperature level of a power source of an analyte monitoring device;
determining a level of power remaining in the power source of the analyte monitoring device; and
selectively deactivating at least one component of the analyte monitoring device when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
2. The method of claim 1, wherein the at least one component is a display.
3. The method of claim 2, wherein the display is an organic light emitting diode (OLED) display.
4. The method of claim 1 , wherein the at least one component is a test strip interface.
5. The method of claim 1, wherein the at least one component is a memory device.
6. The method of claim 5, wherein the memory device is a flash memory device.
7. The method of claim 1 , wherein the predetermined temperature threshold is about zero degrees Celsius.
8. The method of claim 1 , wherein the predetermined temperature threshold is about negative five degrees Celsius.
9. The method of claim 1 wherein the predetermined power threshold is about 3.6V.
10. The method of claim 1 wherein the predetermined power threshold is about
3.7V.
11. The method of claim 1 , wherein selectively deactivating the at least one component comprises determining an amount of power needed by the at least one component and deactivating the at least one component when the determined amount of power exceeds a threshold level.
12. An apparatus, comprising:
one or more processors; and
a memory operatively coupled to the one or more processors, the memory for storing instructions which, when executed by the one or more processors, causes the one or more processors to determine a temperature level of a power source of the apparatus, determine a level of power remaining in the power source of the apparatus, and selectively deactivate at least one component of the apparatus when at least one of the temperature level of the power source reaches a predetermined temperature threshold or when the level of power remaining in the power source reaches a predetermined power threshold.
13. The apparatus of claim 12, wherein the at least one component is a display.
14. The apparatus of claim 13, wherein the display is an organic light emitting diode (OLED) display.
15. The apparatus of claim 12, wherein the at least one component is a test strip interface.
16. The apparatus of claim 12, wherein the at least one component is a memory device.
17. The apparatus of claim 16, wherein the memory device is a flash memory device.
18. The apparatus of claim 12, wherein the predetermined temperature threshold is about zero degrees Celsius.
19. The apparatus of claim 12, wherein the predetermined temperature threshold is about negative five degrees Celsius.
20. The apparatus of claim 12 wherein the predetermined power threshold is about 3.6V.
21. The apparatus of claim 12 wherein the predetermined power threshold is about
3.7V.
22. The apparatus of claim 12, wherein the memory for storing instructions which, when executed by the one or more processors, causes the one or more processors to selectively deactivate the at least one component in response to determining that an amount of power needed by the at least one component exceeds a threshold level.
23. A method comprising :
providing a receiving unit comprising a radio frequency (RF) receiver;
receiving a signal relating to an analyte concentration of a patient;
determining a time window for receiving a subsequent signal corresponding to additional analyte concentrations of the patient; and
selectively deactivating at least one of an antenna of the receiving unit or at least one component of the receiving unit during the determined time window.
24. The method of claim 23, wherein the antenna is deactivated using a switch.
25. The method of claim 23, wherein the at least one component is a display.
26. The method of claim 25, wherein the display is an organic light emitting diode (OLED) display.
27. The method of claim 23, wherein the at least one component is a test strip interface.
- -
28. The method of claim 23, further comprising determining a transmission range between the receiving unit and the transmitter.
29. The method of claim 28, further comprising deactivating the antenna when the determined transmission range is within a predetermined transmission range threshold.
30. The method of claim 28, wherein the transmission range is based on a strength of the signal.
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Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN108025278A (en) * | 2015-02-24 | 2018-05-11 | 实验风格创意有限公司 | System and method for adjusting the power level in monitoring device |
US11690538B2 (en) | 2013-12-16 | 2023-07-04 | Dexcom, Inc. | Systems and methods for monitoring and managing life of a battery in an analyte sensor system worn by a user |
Families Citing this family (50)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8771183B2 (en) | 2004-02-17 | 2014-07-08 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US7697967B2 (en) | 2005-12-28 | 2010-04-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US11298058B2 (en) | 2005-12-28 | 2022-04-12 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor insertion |
US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
US20080199894A1 (en) | 2007-02-15 | 2008-08-21 | Abbott Diabetes Care, Inc. | Device and method for automatic data acquisition and/or detection |
US8239166B2 (en) | 2007-05-14 | 2012-08-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
US8591410B2 (en) | 2008-05-30 | 2013-11-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing glycemic control |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US8986208B2 (en) * | 2008-09-30 | 2015-03-24 | Abbott Diabetes Care Inc. | Analyte sensor sensitivity attenuation mitigation |
US9184490B2 (en) | 2009-05-29 | 2015-11-10 | Abbott Diabetes Care Inc. | Medical device antenna systems having external antenna configurations |
WO2011014851A1 (en) | 2009-07-31 | 2011-02-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte monitoring system calibration accuracy |
WO2011026148A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
ES2912584T3 (en) | 2009-08-31 | 2022-05-26 | Abbott Diabetes Care Inc | A glucose monitoring system and method |
US9041730B2 (en) * | 2010-02-12 | 2015-05-26 | Dexcom, Inc. | Receivers for analyzing and displaying sensor data |
US8239582B2 (en) * | 2010-05-27 | 2012-08-07 | Cilag Gmbh International | Hand-held test meter with disruption avoidance circuitry |
EP4333325A2 (en) | 2010-09-29 | 2024-03-06 | Dexcom, Inc. | Advanced continuous analyte monitoring system |
US8603014B2 (en) * | 2010-10-05 | 2013-12-10 | Cerevast Therapeutics, Inc. | Hands-free operator-independent transcranial ultrasound apparatus and methods |
US8588687B2 (en) | 2010-10-15 | 2013-11-19 | Roche Diagnostics Operations, Inc. | Coexistence of multiple radios in a medical device |
US8849459B2 (en) | 2010-10-15 | 2014-09-30 | Roche Diagnostics Operations, Inc. | Power management system for a handheld medical device |
US8380999B1 (en) * | 2010-12-20 | 2013-02-19 | Amazon Technologies, Inc. | Power management for electronic devices |
US10136845B2 (en) | 2011-02-28 | 2018-11-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods associated with analyte monitoring devices and devices incorporating the same |
US8710993B2 (en) | 2011-11-23 | 2014-04-29 | Abbott Diabetes Care Inc. | Mitigating single point failure of devices in an analyte monitoring system and methods thereof |
KR101795846B1 (en) * | 2012-01-19 | 2017-11-08 | 나이키 이노베이트 씨.브이. | Power management in an activity monitoring device |
RU2014143774A (en) * | 2012-03-30 | 2016-05-27 | Лайфскэн Скотлэнд Лимитед | METHOD AND SYSTEM FOR DETERMINING AND STORING THE BATTERY STATUS IN MEDICAL MONITORING |
EP3395252A1 (en) | 2012-08-30 | 2018-10-31 | Abbott Diabetes Care, Inc. | Dropout detection in continuous analyte monitoring data during data excursions |
US9968306B2 (en) | 2012-09-17 | 2018-05-15 | Abbott Diabetes Care Inc. | Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems |
EP2716213A1 (en) * | 2012-10-02 | 2014-04-09 | Doro AB | Improved measuring in a mobile terminal |
US20140118160A1 (en) * | 2012-10-30 | 2014-05-01 | Quantitative Sampling Technologies, LLC | Controller for supervising data acquisition devices |
US9872641B2 (en) * | 2012-11-29 | 2018-01-23 | Abbott Diabetes Care Inc. | Methods, devices, and systems related to analyte monitoring |
US9585563B2 (en) | 2012-12-31 | 2017-03-07 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US9730620B2 (en) | 2012-12-31 | 2017-08-15 | Dexcom, Inc. | Remote monitoring of analyte measurements |
US9445445B2 (en) | 2013-03-14 | 2016-09-13 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
US9931036B2 (en) | 2013-03-14 | 2018-04-03 | Dexcom, Inc. | Systems and methods for processing and transmitting sensor data |
KR101456591B1 (en) * | 2013-03-26 | 2014-10-31 | 경북대학교 산학협력단 | Bio-signal measuring watch and method for measuring bio-signal |
EP2997882A4 (en) * | 2013-05-13 | 2016-05-11 | Zd Medical Inc | Vascular image positioning system |
US10411693B2 (en) * | 2014-10-28 | 2019-09-10 | Infineon Technologies Ag | Methods and circuits for improved reliability of power devices operating under repetitive thermal stress |
TWI536026B (en) | 2015-06-25 | 2016-06-01 | 財團法人工業技術研究院 | Apparatus, system and method for wireless batch calibration |
WO2017011346A1 (en) | 2015-07-10 | 2017-01-19 | Abbott Diabetes Care Inc. | System, device and method of dynamic glucose profile response to physiological parameters |
US10231655B2 (en) | 2015-12-21 | 2019-03-19 | Dexcom, Inc. | Continuous analyte monitoring system power conservation |
EP3397140A4 (en) | 2015-12-28 | 2019-08-21 | Dexcom, Inc. | Systems and methods for remote and host monitoring communications |
CA3133253A1 (en) | 2016-03-31 | 2017-10-05 | Dexcom, Inc. | Systems and methods for display device and sensor electronics unit communication |
CN109922711B (en) * | 2016-07-15 | 2022-08-19 | 哥特科学股份有限公司 | Electronic single-use chemical diagnostic device |
EP3558117A1 (en) | 2016-12-20 | 2019-10-30 | Abbott Diabetes Care Inc. | Systems, devices and methods for wireless communications in analyte monitoring devices |
US11596330B2 (en) | 2017-03-21 | 2023-03-07 | Abbott Diabetes Care Inc. | Methods, devices and system for providing diabetic condition diagnosis and therapy |
US10517134B2 (en) | 2017-05-11 | 2019-12-24 | Pacesetter, Inc. | Method and system for managing communication between external and implantable devices |
US10782352B2 (en) * | 2018-04-25 | 2020-09-22 | Lifescan Ip Holdings, Llc | Portable test meter with backlight battery depletion monitoring |
US20230091124A1 (en) * | 2021-09-17 | 2023-03-23 | Know Labs, Inc. | Noise reduction in non-invasive radio frequency analyte sensors |
USD1013544S1 (en) | 2022-04-29 | 2024-02-06 | Biolinq Incorporated | Wearable sensor |
USD1012744S1 (en) | 2022-05-16 | 2024-01-30 | Biolinq Incorporated | Wearable sensor with illuminated display |
Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5581206A (en) * | 1995-07-28 | 1996-12-03 | Micron Quantum Devices, Inc. | Power level detection circuit |
US5659454A (en) * | 1993-12-01 | 1997-08-19 | Neopost Industrie | Thermal protection apparatus for a secure electronic appliance, in particular a postage meter |
US6937222B2 (en) * | 2001-01-18 | 2005-08-30 | Sharp Kabushiki Kaisha | Display, portable device, and substrate |
US7228162B2 (en) * | 2003-01-13 | 2007-06-05 | Isense Corporation | Analyte sensor |
US7408132B2 (en) * | 2004-11-08 | 2008-08-05 | Rrc Power Solutions Gmbh | Temperature sensor for power supply |
US20080278332A1 (en) * | 2007-05-08 | 2008-11-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods |
Family Cites Families (1617)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5935099A (en) | 1992-09-09 | 1999-08-10 | Sims Deltec, Inc. | Drug pump systems and methods |
US2755036A (en) | 1953-07-03 | 1956-07-17 | Terho Mikko Jooseppi | Cable drum |
US3260656A (en) | 1962-09-27 | 1966-07-12 | Corning Glass Works | Method and apparatus for electrolytically determining a species in a fluid |
US3304413A (en) | 1963-03-26 | 1967-02-14 | Hewlett Packard Co | Cardiac output computer |
GB1191363A (en) | 1968-02-19 | 1970-05-13 | Pavelle Ltd | Improvements in or relating to Electronic Thermostats. |
US3653841A (en) | 1969-12-19 | 1972-04-04 | Hoffmann La Roche | Methods and compositions for determining glucose in blood |
US3651318A (en) | 1970-01-26 | 1972-03-21 | Jan A Czekajewski | Cardiac output computer |
US3776832A (en) | 1970-11-10 | 1973-12-04 | Energetics Science | Electrochemical detection cell |
US3719564A (en) | 1971-05-10 | 1973-03-06 | Philip Morris Inc | Method of determining a reducible gas concentration and sensor therefor |
US3698386A (en) | 1971-07-16 | 1972-10-17 | Robert Fried | Cardiac rhythm computer device |
US3768014A (en) | 1972-01-28 | 1973-10-23 | Gen Electric | Cardiac pacemaker rate/interval computer system |
US3837339A (en) | 1972-02-03 | 1974-09-24 | Whittaker Corp | Blood glucose level monitoring-alarm system and method therefor |
US3949388A (en) | 1972-11-13 | 1976-04-06 | Monitron Industries, Inc. | Physiological sensor and transmitter |
US3908657A (en) | 1973-01-15 | 1975-09-30 | Univ Johns Hopkins | System for continuous withdrawal of blood |
GB1394171A (en) | 1973-05-16 | 1975-05-14 | Whittaker Corp | Blood glucose level monitoring-alarm system and method therefor |
US4100048A (en) | 1973-09-20 | 1978-07-11 | U.S. Philips Corporation | Polarographic cell |
US3926760A (en) | 1973-09-28 | 1975-12-16 | Du Pont | Process for electrophoretic deposition of polymer |
US4003379A (en) | 1974-04-23 | 1977-01-18 | Ellinwood Jr Everett H | Apparatus and method for implanted self-powered medication dispensing |
US3919051A (en) | 1974-07-11 | 1975-11-11 | Honeywell Inc | Biological analyzer and method |
US3972320A (en) | 1974-08-12 | 1976-08-03 | Gabor Ujhelyi Kalman | Patient monitoring system |
US4245634A (en) | 1975-01-22 | 1981-01-20 | Hospital For Sick Children | Artificial beta cell |
US4036749A (en) | 1975-04-30 | 1977-07-19 | Anderson Donald R | Purification of saline water |
US4021718A (en) | 1975-08-21 | 1977-05-03 | General Electric Company | Battery monitoring apparatus |
US3979274A (en) | 1975-09-24 | 1976-09-07 | The Yellow Springs Instrument Company, Inc. | Membrane for enzyme electrodes |
US4031449A (en) | 1975-11-20 | 1977-06-21 | Arthur D. Little, Inc. | Electromagnetically coupled battery charger |
US4016866A (en) | 1975-12-18 | 1977-04-12 | General Electric Company | Implantable electrochemical sensor |
US4193026A (en) | 1976-04-18 | 1980-03-11 | Curtis Instruments, Inc. | Method and apparatus for measuring the state of charge of a battery by monitoring reductions in voltage |
US4055175A (en) | 1976-05-07 | 1977-10-25 | Miles Laboratories, Inc. | Blood glucose control apparatus |
DE2625834B2 (en) | 1976-06-09 | 1978-10-12 | Boehringer Mannheim Gmbh, 6800 Mannheim | Method for the determination of substrates or enzyme activities |
US4059406A (en) | 1976-07-12 | 1977-11-22 | E D T Supplies Limited | Electrochemical detector system |
GB1579690A (en) | 1976-08-16 | 1980-11-19 | Medtronic Inc | Electromedical apparatus |
US4076596A (en) | 1976-10-07 | 1978-02-28 | Leeds & Northrup Company | Apparatus for electrolytically determining a species in a fluid and method of use |
US4129128A (en) | 1977-02-23 | 1978-12-12 | Mcfarlane Richard H | Securing device for catheter placement assembly |
FR2387659A1 (en) | 1977-04-21 | 1978-11-17 | Armines | GLYCEMIA CONTROL AND REGULATION DEVICE |
US4098574A (en) | 1977-08-01 | 1978-07-04 | Eastman Kodak Company | Glucose detection system free from fluoride-ion interference |
US4178916A (en) | 1977-09-26 | 1979-12-18 | Mcnamara Elger W | Diabetic insulin alarm system |
JPS5912135B2 (en) | 1977-09-28 | 1984-03-21 | 松下電器産業株式会社 | enzyme electrode |
US4154231A (en) | 1977-11-23 | 1979-05-15 | Russell Robert B | System for non-invasive cardiac diagnosis |
US4151845A (en) | 1977-11-25 | 1979-05-01 | Miles Laboratories, Inc. | Blood glucose control apparatus |
JPS5921500B2 (en) | 1978-01-28 | 1984-05-21 | 東洋紡績株式会社 | Enzyme membrane for oxygen electrode |
DK151000C (en) | 1978-02-17 | 1988-06-13 | Radiometer As | PROCEDURE AND APPARATUS FOR DETERMINING A PATIENT'S IN VIVO PLASMA-PH VALUE |
US4172770A (en) | 1978-03-27 | 1979-10-30 | Technicon Instruments Corporation | Flow-through electrochemical system analytical method |
DE2817363C2 (en) | 1978-04-20 | 1984-01-26 | Siemens AG, 1000 Berlin und 8000 München | Method for determining the concentration of sugar and a suitable electrocatalytic sugar sensor |
US4958632A (en) | 1978-07-20 | 1990-09-25 | Medtronic, Inc. | Adaptable, digital computer controlled cardiac pacemaker |
US4344438A (en) | 1978-08-02 | 1982-08-17 | The United States Of America As Represented By The Department Of Health, Education And Welfare | Optical sensor of plasma constituents |
JPS55500431A (en) | 1978-08-15 | 1980-07-17 | ||
HU177369B (en) | 1978-09-08 | 1981-09-28 | Radelkis Electrokemiai | Industrial molecule-selective sensing device and method for producing same |
EP0010375B1 (en) | 1978-10-02 | 1983-07-20 | Xerox Corporation | Electrostatographic processing system |
US4240438A (en) | 1978-10-02 | 1980-12-23 | Wisconsin Alumni Research Foundation | Method for monitoring blood glucose levels and elements |
JPS584982B2 (en) | 1978-10-31 | 1983-01-28 | 松下電器産業株式会社 | enzyme electrode |
AU530979B2 (en) | 1978-12-07 | 1983-08-04 | Aus. Training Aids Pty. Ltd., | Detecting position of bullet fired at target |
US4247297A (en) | 1979-02-23 | 1981-01-27 | Miles Laboratories, Inc. | Test means and method for interference resistant determination of oxidizing substances |
US4271449A (en) | 1979-04-04 | 1981-06-02 | Rockwell International Corporation | Method and apparatus for protecting alternating current circuits |
US4573994A (en) | 1979-04-27 | 1986-03-04 | The Johns Hopkins University | Refillable medication infusion apparatus |
US4365637A (en) | 1979-07-05 | 1982-12-28 | Dia-Med, Inc. | Perspiration indicating alarm for diabetics |
CS210174B1 (en) | 1979-07-12 | 1982-01-29 | Ivan Emmer | Method of making the electric hygrometric sensor |
US4458686A (en) | 1979-08-02 | 1984-07-10 | Children's Hospital Medical Center | Cutaneous methods of measuring body substances |
US4401122A (en) | 1979-08-02 | 1983-08-30 | Children's Hospital Medical Center | Cutaneous methods of measuring body substances |
US4467811A (en) | 1979-08-02 | 1984-08-28 | Children's Hospital Medical Center | Method of polarographic analysis of lactic acid and lactate |
US4293396A (en) | 1979-09-27 | 1981-10-06 | Prototech Company | Thin carbon-cloth-based electrocatalytic gas diffusion electrodes, and electrochemical cells comprising the same |
DE3114441A1 (en) | 1980-04-11 | 1982-03-04 | Radiometer A/S, 2400 Koebenhavn | ELECTROCHEMICAL MEASURING ELECTRODE DEVICE |
US4450842A (en) | 1980-04-25 | 1984-05-29 | Cordis Corporation | Solid state reference electrode |
US4340458A (en) | 1980-06-02 | 1982-07-20 | Joslin Diabetes Center, Inc. | Glucose sensor |
CA1169323A (en) | 1980-06-03 | 1984-06-19 | Anthony M. Albisser | Insulin infusion device |
US4331869A (en) | 1980-06-23 | 1982-05-25 | Capintec, Inc. | Dynamic cardiac quality assurance phantom system and method |
AU546785B2 (en) | 1980-07-23 | 1985-09-19 | Commonwealth Of Australia, The | Open-loop controlled infusion of diabetics |
US4356074A (en) | 1980-08-25 | 1982-10-26 | The Yellow Springs Instrument Company, Inc. | Substrate specific galactose oxidase enzyme electrodes |
US4404066A (en) | 1980-08-25 | 1983-09-13 | The Yellow Springs Instrument Company | Method for quantitatively determining a particular substrate catalyzed by a multisubstrate enzyme |
USRE32947E (en) | 1980-09-30 | 1989-06-13 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4352960A (en) | 1980-09-30 | 1982-10-05 | Baptist Medical Center Of Oklahoma, Inc. | Magnetic transcutaneous mount for external device of an associated implant |
US4444892A (en) | 1980-10-20 | 1984-04-24 | Malmros Mark K | Analytical device having semiconductive organic polymeric element associated with analyte-binding substance |
US4425920A (en) | 1980-10-24 | 1984-01-17 | Purdue Research Foundation | Apparatus and method for measurement and control of blood pressure |
US4407959A (en) | 1980-10-29 | 1983-10-04 | Fuji Electric Co., Ltd. | Blood sugar analyzing apparatus |
US4420564A (en) | 1980-11-21 | 1983-12-13 | Fuji Electric Company, Ltd. | Blood sugar analyzer having fixed enzyme membrane sensor |
US4327725A (en) | 1980-11-25 | 1982-05-04 | Alza Corporation | Osmotic device with hydrogel driving member |
US4483924A (en) | 1980-12-09 | 1984-11-20 | Fuji Electric Company, Ltd. | System for controlling a printer in a blood sugar analyzer |
US4390621A (en) | 1980-12-15 | 1983-06-28 | Miles Laboratories, Inc. | Method and device for detecting glucose concentration |
US4436094A (en) | 1981-03-09 | 1984-03-13 | Evreka, Inc. | Monitor for continuous in vivo measurement of glucose concentration |
US4427004A (en) | 1981-03-16 | 1984-01-24 | Viridan Inc. | Annular flow entrainment nebulizer |
EP0064369B1 (en) | 1981-04-24 | 1986-10-08 | Kabushiki Kaisha Kyoto Daiichi Kagaku | A device for automatically and continuously measuring the constituent parts of blood |
AT369254B (en) | 1981-05-07 | 1982-12-27 | Otto Dipl Ing Dr Tech Prohaska | MEDICAL PROBE |
FR2508305B1 (en) | 1981-06-25 | 1986-04-11 | Slama Gerard | DEVICE FOR CAUSING A LITTLE BITE TO COLLECT A BLOOD DROP |
US4440175A (en) | 1981-08-10 | 1984-04-03 | University Patents, Inc. | Membrane electrode for non-ionic species |
US4445090A (en) | 1981-08-26 | 1984-04-24 | Towmotor Corporation | Voltage level monitoring and indicating apparatus |
DE3138194A1 (en) | 1981-09-25 | 1983-04-14 | Basf Ag, 6700 Ludwigshafen | WATER-INSOLUBLE POROESES PROTEIN MATERIAL, THEIR PRODUCTION AND USE |
DE3278334D1 (en) | 1981-10-23 | 1988-05-19 | Genetics Int Inc | Sensor for components of a liquid mixture |
US4431004A (en) | 1981-10-27 | 1984-02-14 | Bessman Samuel P | Implantable glucose sensor |
US4418148A (en) | 1981-11-05 | 1983-11-29 | Miles Laboratories, Inc. | Multilayer enzyme electrode membrane |
JPS5886083A (en) | 1981-11-12 | 1983-05-23 | Wako Pure Chem Ind Ltd | Stabilizing agent for glycerol-3-phosphoric acid oxidase |
US4494950A (en) | 1982-01-19 | 1985-01-22 | The Johns Hopkins University | Plural module medication delivery system |
JPS58153154A (en) | 1982-03-09 | 1983-09-12 | Ajinomoto Co Inc | Qualified electrode |
US4417588A (en) | 1982-03-22 | 1983-11-29 | Critikon, Inc. | Apparatus and method for initiating cardiac output computations |
US4581336A (en) | 1982-04-26 | 1986-04-08 | Uop Inc. | Surface-modified electrodes |
FI831399L (en) | 1982-04-29 | 1983-10-30 | Agripat Sa | KONTAKTLINS AV HAERDAD POLYVINYL ALCOHOL |
DE3221339A1 (en) | 1982-06-05 | 1983-12-08 | Basf Ag, 6700 Ludwigshafen | METHOD FOR THE ELECTROCHEMICAL HYDRATION OF NICOTINAMIDADENINE-DINUCLEOTIDE |
US4427770A (en) | 1982-06-14 | 1984-01-24 | Miles Laboratories, Inc. | High glucose-determining analytical element |
US4633881A (en) | 1982-07-01 | 1987-01-06 | The General Hospital Corporation | Ambulatory ventricular function monitor |
EP0098592A3 (en) | 1982-07-06 | 1985-08-21 | Fujisawa Pharmaceutical Co., Ltd. | Portable artificial pancreas |
US4509531A (en) | 1982-07-28 | 1985-04-09 | Teledyne Industries, Inc. | Personal physiological monitor |
DE3228551A1 (en) | 1982-07-30 | 1984-02-02 | Siemens AG, 1000 Berlin und 8000 München | METHOD FOR DETERMINING SUGAR CONCENTRATION |
US4534356A (en) | 1982-07-30 | 1985-08-13 | Diamond Shamrock Chemicals Company | Solid state transcutaneous blood gas sensors |
US4571292A (en) | 1982-08-12 | 1986-02-18 | Case Western Reserve University | Apparatus for electrochemical measurements |
US4464170A (en) | 1982-09-29 | 1984-08-07 | Miles Laboratories, Inc. | Blood glucose control apparatus and method |
GB2128453A (en) | 1982-10-08 | 1984-04-26 | Philips Electronic Associated | System identification in communications systems |
US4595479A (en) | 1982-11-09 | 1986-06-17 | Ajinomoto Co., Inc. | Modified electrode |
US4552840A (en) | 1982-12-02 | 1985-11-12 | California And Hawaiian Sugar Company | Enzyme electrode and method for dextran analysis |
US4527240A (en) | 1982-12-29 | 1985-07-02 | Kvitash Vadim I | Balascopy method for detecting and rapidly evaluating multiple imbalances within multi-parametric systems |
CA1231016A (en) | 1983-01-23 | 1988-01-05 | Amir Porat | Syringe |
US4461691A (en) | 1983-02-10 | 1984-07-24 | The United States Of America As Represented By The United States Department Of Energy | Organic conductive films for semiconductor electrodes |
US4679562A (en) | 1983-02-16 | 1987-07-14 | Cardiac Pacemakers, Inc. | Glucose sensor |
WO1984003562A1 (en) | 1983-03-11 | 1984-09-13 | Matsushita Electric Ind Co Ltd | Biosensor |
FR2544525A1 (en) | 1983-04-12 | 1984-10-19 | Simatec Sarl | PORTABLE APPARATUS FOR SEIZING AND PROCESSING INFORMATION RELATING TO THE HEALTH OF A PERSON |
IT1170375B (en) | 1983-04-19 | 1987-06-03 | Giuseppe Bombardieri | Implantable device for measuring body fluid parameters |
CA1220818A (en) | 1983-05-05 | 1987-04-21 | Hugh A.O. Hill | Assay techniques utilising specific binding agents |
CA1226036A (en) | 1983-05-05 | 1987-08-25 | Irving J. Higgins | Analytical equipment and sensor electrodes therefor |
CA1219040A (en) | 1983-05-05 | 1987-03-10 | Elliot V. Plotkin | Measurement of enzyme-catalysed reactions |
CA1218704A (en) | 1983-05-05 | 1987-03-03 | Graham Davis | Assay systems using more than one enzyme |
US5509410A (en) | 1983-06-06 | 1996-04-23 | Medisense, Inc. | Strip electrode including screen printing of a single layer |
GB2154003B (en) | 1983-12-16 | 1988-02-17 | Genetics Int Inc | Diagnostic aid |
US5682884A (en) | 1983-05-05 | 1997-11-04 | Medisense, Inc. | Strip electrode with screen printing |
US4484987A (en) | 1983-05-19 | 1984-11-27 | The Regents Of The University Of California | Method and membrane applicable to implantable sensor |
US4650547A (en) | 1983-05-19 | 1987-03-17 | The Regents Of The University Of California | Method and membrane applicable to implantable sensor |
US4569589A (en) | 1983-05-25 | 1986-02-11 | University Of Pennsylvania | Lung water computer system |
US4524114A (en) | 1983-07-05 | 1985-06-18 | Allied Corporation | Bifunctional air electrode |
US4538616A (en) | 1983-07-25 | 1985-09-03 | Robert Rogoff | Blood sugar level sensing and monitoring transducer |
US4543955A (en) | 1983-08-01 | 1985-10-01 | Cordis Corporation | System for controlling body implantable action device |
US4655880A (en) | 1983-08-01 | 1987-04-07 | Case Western Reserve University | Apparatus and method for sensing species, substances and substrates using oxidase |
SE8305704D0 (en) | 1983-10-18 | 1983-10-18 | Leo Ab | Cuvette |
US4560534A (en) | 1983-11-02 | 1985-12-24 | Miles Laboratories, Inc. | Polymer catalyst transducers |
GB8417949D0 (en) | 1984-07-13 | 1984-08-15 | Palmer G C | Sampling fluid |
US4522690A (en) | 1983-12-01 | 1985-06-11 | Honeywell Inc. | Electrochemical sensing of carbon monoxide |
DE3479522D1 (en) | 1983-12-16 | 1989-09-28 | Medisense Inc | Assay for nucleic acids |
US4685903A (en) | 1984-01-06 | 1987-08-11 | Pacesetter Infusion, Ltd. | External infusion pump apparatus |
US4583035A (en) | 1984-03-05 | 1986-04-15 | Sloan Albert H | Apparatus for monitoring and charging electric storage battery |
SU1281988A1 (en) | 1984-03-15 | 1987-01-07 | Институт биохимии АН ЛитССР | Electrochemical transducer for measuring glucose concentration |
US4684537A (en) | 1984-04-30 | 1987-08-04 | R. E. Stiftung | Process for the sensitization of an oxidation/reduction photocatalyst, and photocatalyst thus obtained |
NL8401536A (en) | 1984-05-11 | 1985-12-02 | Medscan B V I O | BLOOD SAMPLING UNIT. |
US5141868A (en) | 1984-06-13 | 1992-08-25 | Internationale Octrooi Maatschappij "Octropa" Bv | Device for use in chemical test procedures |
CA1261256A (en) | 1984-06-13 | 1989-09-26 | Ian A. Shanks | Devices for use in chemical test procedures |
GB8417301D0 (en) | 1984-07-06 | 1984-08-08 | Serono Diagnostics Ltd | Assay |
DK8601218A (en) | 1984-07-18 | 1986-03-17 | ||
DE3429596A1 (en) | 1984-08-10 | 1986-02-20 | Siemens AG, 1000 Berlin und 8000 München | DEVICE FOR THE PHYSIOLOGICAL FREQUENCY CONTROL OF A PACEMAKER PROVIDED WITH A PICTURE ELECTRODE |
US4820399A (en) | 1984-08-31 | 1989-04-11 | Shimadzu Corporation | Enzyme electrodes |
CA1254091A (en) | 1984-09-28 | 1989-05-16 | Vladimir Feingold | Implantable medication infusion system |
JPH0134911Y2 (en) | 1984-10-11 | 1989-10-24 | ||
GB2168815A (en) | 1984-11-13 | 1986-06-25 | Genetics Int Inc | Bioelectrochemical assay electrode |
US4721601A (en) | 1984-11-23 | 1988-01-26 | Massachusetts Institute Of Technology | Molecule-based microelectronic devices |
US4936956A (en) | 1984-11-23 | 1990-06-26 | Massachusetts Institute Of Technology | Microelectrochemical devices based on inorganic redox active material and method for sensing |
US4717673A (en) | 1984-11-23 | 1988-01-05 | Massachusetts Institute Of Technology | Microelectrochemical devices |
US5034192A (en) | 1984-11-23 | 1991-07-23 | Massachusetts Institute Of Technology | Molecule-based microelectronic devices |
JPH0617889B2 (en) | 1984-11-27 | 1994-03-09 | 株式会社日立製作所 | Biochemical sensor |
EP0186210B1 (en) | 1984-12-28 | 1992-04-22 | TERUMO KABUSHIKI KAISHA trading as TERUMO CORPORATION | Ion sensor |
GB8500729D0 (en) | 1985-01-11 | 1985-02-13 | Hill H A O | Surface-modified electrode |
US4847785A (en) | 1985-01-22 | 1989-07-11 | International Business Machines Corp. | Interactive display for trend or bar graph |
EP0200321A3 (en) | 1985-03-20 | 1987-03-11 | Ingeborg J. Hochmair | Transcutaneous signal transmission system |
US4627445A (en) | 1985-04-08 | 1986-12-09 | Garid, Inc. | Glucose medical monitoring system |
US5279294A (en) | 1985-04-08 | 1994-01-18 | Cascade Medical, Inc. | Medical diagnostic system |
US4674652A (en) | 1985-04-11 | 1987-06-23 | Aten Edward M | Controlled dispensing device |
US4781798A (en) | 1985-04-19 | 1988-11-01 | The Regents Of The University Of California | Transparent multi-oxygen sensor array and method of using same |
US4671288A (en) | 1985-06-13 | 1987-06-09 | The Regents Of The University Of California | Electrochemical cell sensor for continuous short-term use in tissues and blood |
US5185256A (en) | 1985-06-21 | 1993-02-09 | Matsushita Electric Industrial Co., Ltd. | Method for making a biosensor |
EP0230472B2 (en) | 1985-06-21 | 2000-12-13 | Matsushita Electric Industrial Co., Ltd. | Biosensor and method of manufacturing same |
US4938860A (en) | 1985-06-28 | 1990-07-03 | Miles Inc. | Electrode for electrochemical sensors |
US4835372A (en) | 1985-07-19 | 1989-05-30 | Clincom Incorporated | Patient care system |
EP0231217B1 (en) | 1985-07-23 | 1989-09-06 | Winfried Jean Werding | Thrust regulator comprising a mounting housing |
US4653513A (en) | 1985-08-09 | 1987-03-31 | Dombrowski Mitchell P | Blood sampler |
US4796634A (en) | 1985-08-09 | 1989-01-10 | Lawrence Medical Systems, Inc. | Methods and apparatus for monitoring cardiac output |
US4805624A (en) | 1985-09-09 | 1989-02-21 | The Montefiore Hospital Association Of Western Pa | Low-potential electrochemical redox sensors |
GB8522834D0 (en) | 1985-09-16 | 1985-10-23 | Ici Plc | Sensor |
US4680268A (en) | 1985-09-18 | 1987-07-14 | Children's Hospital Medical Center | Implantable gas-containing biosensor and method for measuring an analyte such as glucose |
US5245314A (en) | 1985-09-18 | 1993-09-14 | Kah Jr Carl L C | Location monitoring system |
US4890620A (en) | 1985-09-20 | 1990-01-02 | The Regents Of The University Of California | Two-dimensional diffusion glucose substrate sensing electrode |
US5007427A (en) | 1987-05-07 | 1991-04-16 | Capintec, Inc. | Ambulatory physiological evaluation system including cardiac monitoring |
US5111818A (en) | 1985-10-08 | 1992-05-12 | Capintec, Inc. | Ambulatory physiological evaluation system including cardiac monitoring |
US5140393A (en) | 1985-10-08 | 1992-08-18 | Sharp Kabushiki Kaisha | Sensor device |
US4920969A (en) | 1985-10-08 | 1990-05-01 | Capintec, Inc. | Ambulatory physiological evaluation system including cardiac monitoring |
US4627908A (en) | 1985-10-24 | 1986-12-09 | Chevron Research Company | Process for stabilizing lube base stocks derived from bright stock |
US4830959A (en) | 1985-11-11 | 1989-05-16 | Medisense, Inc. | Electrochemical enzymic assay procedures |
GB8529300D0 (en) | 1985-11-28 | 1986-01-02 | Ici Plc | Membrane |
US4857713A (en) | 1986-02-14 | 1989-08-15 | Brown Jack D | Hospital error avoidance system |
US4776944A (en) | 1986-03-20 | 1988-10-11 | Jiri Janata | Chemical selective sensors utilizing admittance modulated membranes |
WO1987006040A1 (en) | 1986-03-31 | 1987-10-08 | Puritan-Bennett Corporation | Computer gated positive expiratory pressure system |
US4685463A (en) | 1986-04-03 | 1987-08-11 | Williams R Bruce | Device for continuous in vivo measurement of blood glucose concentrations |
GB8608700D0 (en) | 1986-04-10 | 1986-05-14 | Genetics Int Inc | Measurement of electroactive species in solution |
US4726378A (en) | 1986-04-11 | 1988-02-23 | Minnesota Mining And Manufacturing Company | Adjustable magnetic supercutaneous device and transcutaneous coupling apparatus |
US4757022A (en) | 1986-04-15 | 1988-07-12 | Markwell Medical Institute, Inc. | Biological fluid measuring device |
US4994167A (en) | 1986-04-15 | 1991-02-19 | Markwell Medical Institute, Inc. | Biological fluid measuring device |
US4909908A (en) | 1986-04-24 | 1990-03-20 | Pepi Ross | Electrochemical cncentration detector method |
DE3614821A1 (en) | 1986-05-02 | 1987-11-05 | Siemens Ag | IMPLANTABLE, CALIBRABLE MEASURING DEVICE FOR A BODY SUBSTANCE AND CALIBRATION METHOD |
US4703756A (en) | 1986-05-06 | 1987-11-03 | The Regents Of The University Of California | Complete glucose monitoring system with an implantable, telemetered sensor module |
US4731726A (en) | 1986-05-19 | 1988-03-15 | Healthware Corporation | Patient-operated glucose monitor and diabetes management system |
GB8612861D0 (en) | 1986-05-27 | 1986-07-02 | Cambridge Life Sciences | Immobilised enzyme biosensors |
US4750496A (en) | 1987-01-28 | 1988-06-14 | Xienta, Inc. | Method and apparatus for measuring blood glucose concentration |
US4969468A (en) | 1986-06-17 | 1990-11-13 | Alfred E. Mann Foundation For Scientific Research | Electrode array for use in connection with a living body and method of manufacture |
US4837049A (en) | 1986-06-17 | 1989-06-06 | Alfred E. Mann Foundation For Scientific Research | Method of making an electrode array |
US4911794A (en) | 1986-06-20 | 1990-03-27 | Molecular Devices Corporation | Measuring with zero volume cell |
US5001054A (en) | 1986-06-26 | 1991-03-19 | Becton, Dickinson And Company | Method for monitoring glucose |
JPS636451A (en) | 1986-06-27 | 1988-01-12 | Terumo Corp | Enzyme sensor |
US4803625A (en) | 1986-06-30 | 1989-02-07 | Buddy Systems, Inc. | Personal health monitor |
US4764416A (en) | 1986-07-01 | 1988-08-16 | Mitsubishi Denki Kabushiki Kaisha | Electric element circuit using oxidation-reduction substances |
US4917800A (en) | 1986-07-07 | 1990-04-17 | Bend Research, Inc. | Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers |
US4784736A (en) | 1986-07-07 | 1988-11-15 | Bend Research, Inc. | Functional, photochemically active, and chemically asymmetric membranes by interfacial polymerization of derivatized multifunctional prepolymers |
US4726716A (en) | 1986-07-21 | 1988-02-23 | Mcguire Thomas V | Fastener for catheter |
GB8618022D0 (en) | 1986-07-23 | 1986-08-28 | Unilever Plc | Electrochemical measurements |
US5049487A (en) | 1986-08-13 | 1991-09-17 | Lifescan, Inc. | Automated initiation of timing of reflectance readings |
US4935346A (en) | 1986-08-13 | 1990-06-19 | Lifescan, Inc. | Minimum procedure system for the determination of analytes |
GB8621061D0 (en) | 1986-09-01 | 1986-10-08 | Hewlett Packard Ltd | User interface simulation |
US4894137A (en) | 1986-09-12 | 1990-01-16 | Omron Tateisi Electronics Co. | Enzyme electrode |
US5055171A (en) | 1986-10-06 | 1991-10-08 | T And G Corporation | Ionic semiconductor materials and applications thereof |
US4897162A (en) | 1986-11-14 | 1990-01-30 | The Cleveland Clinic Foundation | Pulse voltammetry |
JPS63131057A (en) | 1986-11-20 | 1988-06-03 | Terumo Corp | Enzyme sensor |
EP0333779A4 (en) | 1986-12-12 | 1990-02-06 | Metrologic Instr Inc | Bar code reader with digitizer and sequencer. |
DE3700119A1 (en) | 1987-01-03 | 1988-07-14 | Inst Diabetestechnologie Gemei | IMPLANTABLE ELECTROCHEMICAL SENSOR |
US4934369A (en) | 1987-01-30 | 1990-06-19 | Minnesota Mining And Manufacturing Company | Intravascular blood parameter measurement system |
AT391998B (en) | 1987-02-02 | 1990-12-27 | Falko Dr Skrabal | Device for determining the concentration of at least one medicinal substance in living organisms |
EP0278647A3 (en) | 1987-02-09 | 1989-09-20 | AT&T Corp. | Electronchemical processes involving enzymes |
GB2201248B (en) | 1987-02-24 | 1991-04-17 | Ici Plc | Enzyme electrode sensors |
US5002054A (en) | 1987-02-25 | 1991-03-26 | Ash Medical Systems, Inc. | Interstitial filtration and collection device and method for long-term monitoring of physiological constituents of the body |
US4777953A (en) | 1987-02-25 | 1988-10-18 | Ash Medical Systems, Inc. | Capillary filtration and collection method for long-term monitoring of blood constituents |
US4854322A (en) | 1987-02-25 | 1989-08-08 | Ash Medical Systems, Inc. | Capillary filtration and collection device for long-term monitoring of blood constituents |
US4848351A (en) | 1987-03-04 | 1989-07-18 | Sentry Medical Products, Inc. | Medical electrode assembly |
GB2204408A (en) | 1987-03-04 | 1988-11-09 | Plessey Co Plc | Biosensor device |
US4923586A (en) | 1987-03-31 | 1990-05-08 | Daikin Industries, Ltd. | Enzyme electrode unit |
US4935345A (en) | 1987-04-07 | 1990-06-19 | Arizona Board Of Regents | Implantable microelectronic biochemical sensor incorporating thin film thermopile |
US4759828A (en) | 1987-04-09 | 1988-07-26 | Nova Biomedical Corporation | Glucose electrode and method of determining glucose |
US5352348A (en) | 1987-04-09 | 1994-10-04 | Nova Biomedical Corporation | Method of using enzyme electrode |
US4749985A (en) | 1987-04-13 | 1988-06-07 | United States Of America As Represented By The United States Department Of Energy | Functional relationship-based alarm processing |
EP0290683A3 (en) | 1987-05-01 | 1988-12-14 | Diva Medical Systems B.V. | Diabetes management system and apparatus |
US5216597A (en) | 1987-05-01 | 1993-06-01 | Diva Medical Systems Bv | Diabetes therapy management system, apparatus and method |
US5286364A (en) | 1987-06-08 | 1994-02-15 | Rutgers University | Surface-modified electochemical biosensor |
US4822337A (en) | 1987-06-22 | 1989-04-18 | Stanley Newhouse | Insulin delivery method and apparatus |
DE3721237A1 (en) | 1987-06-27 | 1989-01-05 | Boehringer Mannheim Gmbh | DIAGNOSTIC TEST CARRIER AND METHOD FOR THE PRODUCTION THEREOF |
JPH07122624B2 (en) | 1987-07-06 | 1995-12-25 | ダイキン工業株式会社 | Biosensor |
US4874500A (en) | 1987-07-15 | 1989-10-17 | Sri International | Microelectrochemical sensor and sensor array |
GB8718430D0 (en) | 1987-08-04 | 1987-09-09 | Ici Plc | Sensor |
JPS6423155A (en) | 1987-07-17 | 1989-01-25 | Daikin Ind Ltd | Electrode refreshing device for biosensor |
US5135003A (en) | 1987-08-11 | 1992-08-04 | Terumo Kabushiki Kaisha | Automatic sphygmomanometer |
US5037527A (en) | 1987-08-28 | 1991-08-06 | Kanzaki Paper Mfg. Co., Ltd. | Reference electrode and a measuring apparatus using the same |
US4858617A (en) | 1987-09-10 | 1989-08-22 | Ith, Inc. | Cardiac probe enabling use of personal computer for monitoring heart activity or the like |
US4974929A (en) | 1987-09-22 | 1990-12-04 | Baxter International, Inc. | Fiber optical probe connector for physiologic measurement devices |
NL8702370A (en) | 1987-10-05 | 1989-05-01 | Groningen Science Park | METHOD AND SYSTEM FOR GLUCOSE DETERMINATION AND USEABLE MEASURING CELL ASSEMBLY. |
US4845035A (en) | 1987-10-06 | 1989-07-04 | The United States Of America As Represented By The Secretary Of Agriculture | Enzyme immobilization with a hydrolyzed polysaccharide graft copolymer |
US4815469A (en) | 1987-10-08 | 1989-03-28 | Siemens-Pacesetter, Inc. | Implantable blood oxygen sensor and method of use |
GB8725936D0 (en) | 1987-11-05 | 1987-12-09 | Genetics Int Inc | Sensing system |
JPH01140054A (en) | 1987-11-26 | 1989-06-01 | Nec Corp | Glucose sensor |
DK158130C (en) | 1987-11-30 | 1990-09-03 | Uno Plast As | APPARATUS FOR COLLECTION AND MEASUREMENT OF BODY LIQUID |
US4856340A (en) | 1987-12-01 | 1989-08-15 | Minimed Technologies | Pressure diaphragm for a medication infusion system |
US4813424A (en) | 1987-12-23 | 1989-03-21 | University Of New Mexico | Long-life membrane electrode for non-ionic species |
US5073500A (en) | 1988-01-08 | 1991-12-17 | Inax Corporation | Method and apparatus for detecting urinary constituents |
US4890621A (en) | 1988-01-19 | 1990-01-02 | Northstar Research Institute, Ltd. | Continuous glucose monitoring and a system utilized therefor |
US5126247A (en) | 1988-02-26 | 1992-06-30 | Enzymatics, Inc. | Method, system and devices for the assay and detection of biochemical molecules |
US5128015A (en) | 1988-03-15 | 1992-07-07 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
US5108564A (en) | 1988-03-15 | 1992-04-28 | Tall Oak Ventures | Method and apparatus for amperometric diagnostic analysis |
US4957115A (en) | 1988-03-25 | 1990-09-18 | New England Medical Center Hosp. | Device for determining the probability of death of cardiac patients |
EP0359831B2 (en) | 1988-03-31 | 2007-06-20 | Matsushita Electric Industrial Co., Ltd. | Biosensor and process for its production |
US4942127A (en) | 1988-05-06 | 1990-07-17 | Molecular Devices Corporation | Polyredox couples in analyte determinations |
US5206145A (en) | 1988-05-19 | 1993-04-27 | Thorn Emi Plc | Method of measuring the concentration of a substance in a sample solution |
US4874499A (en) | 1988-05-23 | 1989-10-17 | Massachusetts Institute Of Technology | Electrochemical microsensors and method of making such sensors |
US5094951A (en) | 1988-06-21 | 1992-03-10 | Chiron Corporation | Production of glucose oxidase in recombinant systems |
WO1990000367A1 (en) | 1988-07-14 | 1990-01-25 | Bomed Medical Manufacturing, Ltd. | Management of hemodynamic state of a patient |
GB8817421D0 (en) | 1988-07-21 | 1988-08-24 | Medisense Inc | Bioelectrochemical electrodes |
US4925268A (en) | 1988-07-25 | 1990-05-15 | Abbott Laboratories | Fiber-optic physiological probes |
US4954129A (en) | 1988-07-25 | 1990-09-04 | Abbott Laboratories | Hydrodynamic clot flushing |
EP0353328A1 (en) | 1988-08-03 | 1990-02-07 | Dräger Nederland B.V. | A polarographic-amperometric three-electrode sensor |
US5340722A (en) | 1988-08-24 | 1994-08-23 | Avl Medical Instruments Ag | Method for the determination of the concentration of an enzyme substrate and a sensor for carrying out the method |
US4844076A (en) | 1988-08-26 | 1989-07-04 | The Johns Hopkins University | Ingestible size continuously transmitting temperature monitoring pill |
US5264106A (en) | 1988-10-07 | 1993-11-23 | Medisense, Inc. | Enhanced amperometric sensor |
US4995402A (en) | 1988-10-12 | 1991-02-26 | Thorne, Smith, Astill Technologies, Inc. | Medical droplet whole blood and like monitoring |
US4920977A (en) | 1988-10-25 | 1990-05-01 | Becton, Dickinson And Company | Blood collection assembly with lancet and microcollection tube |
GB2225637A (en) | 1988-11-03 | 1990-06-06 | Royal Free Hosp School Med | Portable apparatus for foetal monitors |
GB8825800D0 (en) | 1988-11-04 | 1988-12-07 | Baker J | Cardiac device |
JPH02128152A (en) | 1988-11-08 | 1990-05-16 | Nec Corp | Immobilization of enzyme and biosensor |
CA2002660A1 (en) | 1988-11-10 | 1990-05-10 | Susan J. Mroczkowski | Method for electrical detection of a binding reaction |
US5200051A (en) | 1988-11-14 | 1993-04-06 | I-Stat Corporation | Wholly microfabricated biosensors and process for the manufacture and use thereof |
US5063081A (en) | 1988-11-14 | 1991-11-05 | I-Stat Corporation | Method of manufacturing a plurality of uniform microfabricated sensing devices having an immobilized ligand receptor |
US5360404A (en) | 1988-12-14 | 1994-11-01 | Inviro Medical Devices Ltd. | Needle guard and needle assembly for syringe |
DE3842700A1 (en) | 1988-12-19 | 1990-06-21 | Boehringer Mannheim Gmbh | METHOD FOR PROTEIN IMMOBILIZATION ON A SOLID PHASE, PROTEIN-CARRYING SOLID PHASE PRODUCED THEREOF AND THE USE THEREOF |
FI99250C (en) | 1989-01-10 | 1997-12-29 | Nintendo Co Ltd | System for preventing unauthorized use of external memory |
US5077476A (en) | 1990-06-27 | 1991-12-31 | Futrex, Inc. | Instrument for non-invasive measurement of blood glucose |
US5068536A (en) | 1989-01-19 | 1991-11-26 | Futrex, Inc. | Method for providing custom calibration for near infrared instruments for measurement of blood glucose |
AT392847B (en) | 1989-01-27 | 1991-06-25 | Avl Verbrennungskraft Messtech | SENSOR ELECTRODE ARRANGEMENT |
US5153827A (en) | 1989-01-30 | 1992-10-06 | Omni-Flow, Inc. | An infusion management and pumping system having an alarm handling system |
US5016201A (en) | 1989-02-06 | 1991-05-14 | Bryan Avron I | System for calibrating, monitoring and reporting the status of a pH sensor |
EP0384504A1 (en) | 1989-02-24 | 1990-08-29 | Duphar International Research B.V | Detection strip for detecting and identifying chemical air contaminants, and portable detection kit comprising said strips |
DE69027233T2 (en) | 1989-03-03 | 1996-10-10 | Edward W Stark | Signal processing method and apparatus |
US5205920A (en) | 1989-03-03 | 1993-04-27 | Noboru Oyama | Enzyme sensor and method of manufacturing the same |
JPH02298855A (en) | 1989-03-20 | 1990-12-11 | Assoc Univ Inc | Electrochemical biosensor using immobilized enzyme and redox polymer |
US5089112A (en) | 1989-03-20 | 1992-02-18 | Associated Universities, Inc. | Electrochemical biosensor based on immobilized enzymes and redox polymers |
US4953552A (en) | 1989-04-21 | 1990-09-04 | Demarzo Arthur P | Blood glucose monitoring system |
EP0396788A1 (en) | 1989-05-08 | 1990-11-14 | Dräger Nederland B.V. | Process and sensor for measuring the glucose content of glucosecontaining fluids |
US5096560A (en) | 1989-05-30 | 1992-03-17 | Mitsubishi Petrochemical Co., Ltd. | Electrode for electrochemical detectors |
US5236567A (en) | 1989-05-31 | 1993-08-17 | Nakano Vinegar Co., Ltd. | Enzyme sensor |
US5139023A (en) | 1989-06-02 | 1992-08-18 | Theratech Inc. | Apparatus and method for noninvasive blood glucose monitoring |
US5198367A (en) | 1989-06-09 | 1993-03-30 | Masuo Aizawa | Homogeneous amperometric immunoassay |
US5016172A (en) | 1989-06-14 | 1991-05-14 | Ramp Comsystems, Inc. | Patient compliance and status monitoring system |
US4899839A (en) | 1989-06-14 | 1990-02-13 | Dessertine Albert L | Compliance and patient status monitoring system and method |
FR2648353B1 (en) | 1989-06-16 | 1992-03-27 | Europhor Sa | MICRODIALYSIS PROBE |
CH677149A5 (en) | 1989-07-07 | 1991-04-15 | Disetronic Ag | |
JPH0737991B2 (en) | 1989-07-13 | 1995-04-26 | 株式会社京都第一科学 | Method for measuring glucose concentration |
US5272060A (en) | 1989-07-13 | 1993-12-21 | Kyoto Daiichi Kagaku Co., Ltd. | Method for determination of glucose concentration in whole blood |
US4986271A (en) | 1989-07-19 | 1991-01-22 | The University Of New Mexico | Vivo refillable glucose sensor |
US4979509A (en) | 1989-07-19 | 1990-12-25 | Northstar Research Institute, Ltd. | Continuous glucose monitoring and a system utilized therefor |
US5431160A (en) | 1989-07-19 | 1995-07-11 | University Of New Mexico | Miniature implantable refillable glucose sensor and material therefor |
US5264104A (en) | 1989-08-02 | 1993-11-23 | Gregg Brian A | Enzyme electrodes |
US5264105A (en) | 1989-08-02 | 1993-11-23 | Gregg Brian A | Enzyme electrodes |
US5262035A (en) | 1989-08-02 | 1993-11-16 | E. Heller And Company | Enzyme electrodes |
US5320725A (en) | 1989-08-02 | 1994-06-14 | E. Heller & Company | Electrode and method for the detection of hydrogen peroxide |
US4944299A (en) | 1989-08-08 | 1990-07-31 | Siemens-Pacesetter, Inc. | High speed digital telemetry system for implantable device |
US4931795A (en) | 1989-08-09 | 1990-06-05 | Alfred E. Mann Foundation | Digital to analog signal converter |
US5101814A (en) | 1989-08-11 | 1992-04-07 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
US5190041A (en) | 1989-08-11 | 1993-03-02 | Palti Yoram Prof | System for monitoring and controlling blood glucose |
DK0415288T3 (en) | 1989-08-25 | 1996-07-22 | Toto Ltd | Toilet apparatus with system for inspection of health conditions |
US5095904A (en) | 1989-09-08 | 1992-03-17 | Cochlear Pty. Ltd. | Multi-peak speech procession |
US5050612A (en) | 1989-09-12 | 1991-09-24 | Matsumura Kenneth N | Device for computer-assisted monitoring of the body |
US5522865A (en) | 1989-09-22 | 1996-06-04 | Alfred E. Mann Foundation For Scientific Research | Voltage/current control system for a human tissue stimulator |
US4991582A (en) | 1989-09-22 | 1991-02-12 | Alfred E. Mann Foundation For Scientific Research | Hermetically sealed ceramic and metal package for electronic devices implantable in living bodies |
US5084828A (en) | 1989-09-29 | 1992-01-28 | Healthtech Services Corp. | Interactive medication delivery system |
FR2652736A1 (en) | 1989-10-06 | 1991-04-12 | Neftel Frederic | IMPLANTABLE DEVICE FOR EVALUATING THE RATE OF GLUCOSE. |
US5036860A (en) | 1989-11-24 | 1991-08-06 | Medical Device Technologies, Inc. | Disposable soft tissue biopsy apparatus |
US4994068A (en) | 1989-11-24 | 1991-02-19 | Unidex, Inc. | Combination sterile pad support and lancet containing lancet disposal element |
EP0429076B1 (en) | 1989-11-24 | 1996-01-31 | Matsushita Electric Industrial Co., Ltd. | Preparation of biosensor |
US5082550A (en) | 1989-12-11 | 1992-01-21 | The United States Of America As Represented By The Department Of Energy | Enzyme electrochemical sensor electrode and method of making it |
US5342789A (en) | 1989-12-14 | 1994-08-30 | Sensor Technologies, Inc. | Method and device for detecting and quantifying glucose in body fluids |
US6040194A (en) | 1989-12-14 | 2000-03-21 | Sensor Technologies, Inc. | Methods and device for detecting and quantifying substances in body fluids |
EP0505494B1 (en) | 1989-12-15 | 1995-07-12 | Boehringer Mannheim Corporation | Redox mediator reagent and biosensor |
US5508171A (en) | 1989-12-15 | 1996-04-16 | Boehringer Mannheim Corporation | Assay method with enzyme electrode system |
US4990845A (en) | 1989-12-18 | 1991-02-05 | Alfred E. Mann Foundation For Scientific Research | Floating current source |
US5051688A (en) | 1989-12-20 | 1991-09-24 | Rohm Co., Ltd. | Crossed coil meter driving device having a plurality of input parameters |
US5036861A (en) | 1990-01-11 | 1991-08-06 | Sembrowich Walter L | Method and apparatus for non-invasively monitoring plasma glucose levels |
US5078854A (en) | 1990-01-22 | 1992-01-07 | Mallinckrodt Sensor Systems, Inc. | Polarographic chemical sensor with external reference electrode |
US5061941A (en) | 1990-02-01 | 1991-10-29 | Checkpoint Systems, Inc. | Composite antenna for electronic article surveillance systems |
US5286362A (en) | 1990-02-03 | 1994-02-15 | Boehringer Mannheim Gmbh | Method and sensor electrode system for the electrochemical determination of an analyte or an oxidoreductase as well as the use of suitable compounds therefor |
US5109850A (en) | 1990-02-09 | 1992-05-05 | Massachusetts Institute Of Technology | Automatic blood monitoring for medication delivery method and apparatus |
US5114678A (en) | 1990-03-21 | 1992-05-19 | Miles Inc. | Device for wiping a reagent strip |
US5501956A (en) | 1990-03-23 | 1996-03-26 | Molecular Devices Corporation | Polyredox couples in analyte determinations |
US5165407A (en) | 1990-04-19 | 1992-11-24 | The University Of Kansas | Implantable glucose sensor |
US5161532A (en) | 1990-04-19 | 1992-11-10 | Teknekron Sensor Development Corporation | Integral interstitial fluid sensor |
DE4014109A1 (en) | 1990-05-02 | 1991-11-07 | Siemens Ag | ELECROCHEMICAL DETERMINATION OF THE OXYGEN CONCENTRATION |
US5059158A (en) | 1990-05-08 | 1991-10-22 | E.B.T., Inc. | Electronic transmission control system for a bicycle |
US5265888A (en) | 1990-06-22 | 1993-11-30 | Nintendo Co., Ltd. | Game apparatus and memory cartridge used therefor |
US5250439A (en) | 1990-07-19 | 1993-10-05 | Miles Inc. | Use of conductive sensors in diagnostic assays |
US5202261A (en) | 1990-07-19 | 1993-04-13 | Miles Inc. | Conductive sensors and their use in diagnostic assays |
US5112455A (en) | 1990-07-20 | 1992-05-12 | I Stat Corporation | Method for analytically utilizing microfabricated sensors during wet-up |
JPH0820412B2 (en) | 1990-07-20 | 1996-03-04 | 松下電器産業株式会社 | Quantitative analysis method and device using disposable sensor |
US5182707A (en) | 1990-07-23 | 1993-01-26 | Healthdyne, Inc. | Apparatus for recording reagent test strip data by comparison to color lights on a reference panel |
US5124661A (en) | 1990-07-23 | 1992-06-23 | I-Stat Corporation | Reusable test unit for simulating electrochemical sensor signals for quality assurance of portable blood analyzer instruments |
US5176662A (en) | 1990-08-23 | 1993-01-05 | Minimed Technologies, Ltd. | Subcutaneous injection set with improved cannula mounting arrangement |
CA2049589A1 (en) | 1990-08-24 | 1992-02-25 | Naoki Tsukamura | Stool-type apparatus for sampling and assay of urine with swingable carriage |
US5120421A (en) | 1990-08-31 | 1992-06-09 | The United States Of America As Represented By The United States Department Of Energy | Electrochemical sensor/detector system and method |
GB9019126D0 (en) | 1990-09-01 | 1990-10-17 | Cranfield Biotech Ltd | Electrochemical biosensor stability |
US5217442A (en) | 1990-09-28 | 1993-06-08 | Minimed Technologies | Aspiration and refill kit for a medication infusion pump |
WO1992005775A1 (en) | 1990-09-28 | 1992-04-16 | Pfizer Inc. | Dispensing device containing a hydrophobic medium |
US5251126A (en) | 1990-10-29 | 1993-10-05 | Miles Inc. | Diabetes data analysis and interpretation method |
US5058592A (en) | 1990-11-02 | 1991-10-22 | Whisler G Douglas | Adjustable mountable doppler ultrasound transducer device |
US5197322A (en) | 1990-11-29 | 1993-03-30 | Minimed Technologies, Ltd. | Pressure reservoir filling process for an implantable medication infusion pump |
US5176644A (en) | 1990-11-29 | 1993-01-05 | Minimed Technologies, Ltd. | Medication infusion pump with improved liquid-vapor pressure reservoir |
JP2646848B2 (en) | 1990-11-30 | 1997-08-27 | 日本電気株式会社 | Glucose sensor measurement method |
ATE155575T1 (en) | 1990-12-12 | 1997-08-15 | Sherwood Medical Co | CALIBRATION OF AN INFRARED THERMOMETER USING AREA CALIBRATION CURVE REPRESENTATION |
NL9002764A (en) | 1990-12-14 | 1992-07-01 | Tno | ELECTRODE, FITTED WITH A POLYMER COATING WITH A REDOX ENZYM BOND TO IT. |
AU1356792A (en) | 1991-01-25 | 1992-08-27 | Markwell Medical Institute, Inc. | Implantable biological fluid measuring device |
FR2673289B1 (en) | 1991-02-21 | 1994-06-17 | Asulab Sa | SENSOR FOR MEASURING THE QUANTITY OF A COMPONENT IN SOLUTION. |
FR2673183B1 (en) | 1991-02-21 | 1996-09-27 | Asulab Sa | MONO, BIS OR TRIS (2,2'-BIPYRIDINE SUBSTITUTED) COMPLEXES OF A SELECTED METAL AMONG IRON, RUTHENIUM, OSMIUM OR VANADIUM AND THEIR PREPARATION PROCESSES. |
US5262305A (en) | 1991-03-04 | 1993-11-16 | E. Heller & Company | Interferant eliminating biosensors |
JPH04278450A (en) | 1991-03-04 | 1992-10-05 | Adam Heller | Biosensor and method for analyzing subject |
US5593852A (en) | 1993-12-02 | 1997-01-14 | Heller; Adam | Subcutaneous glucose electrode |
US5192415A (en) | 1991-03-04 | 1993-03-09 | Matsushita Electric Industrial Co., Ltd. | Biosensor utilizing enzyme and a method for producing the same |
US5469855A (en) | 1991-03-08 | 1995-11-28 | Exergen Corporation | Continuous temperature monitor |
US5135004A (en) | 1991-03-12 | 1992-08-04 | Incontrol, Inc. | Implantable myocardial ischemia monitor and related method |
DE4108804A1 (en) | 1991-03-18 | 1992-09-24 | Lauerer Friedrich | ELECTROMEDICAL PROTECTIVE CIRCUIT |
DE4138702A1 (en) | 1991-03-22 | 1992-09-24 | Madaus Medizin Elektronik | METHOD AND DEVICE FOR THE DIAGNOSIS AND QUANTITATIVE ANALYSIS OF APNOE AND FOR THE SIMULTANEOUS DETERMINATION OF OTHER DISEASES |
GB9107193D0 (en) | 1991-04-05 | 1991-05-22 | Wilson Robert | Analytical devices |
US5208154A (en) | 1991-04-08 | 1993-05-04 | The United States Of America As Represented By The Department Of Energy | Reversibly immobilized biological materials in monolayer films on electrodes |
US5192416A (en) | 1991-04-09 | 1993-03-09 | New Mexico State University Technology Transfer Corporation | Method and apparatus for batch injection analysis |
US5293546A (en) | 1991-04-17 | 1994-03-08 | Martin Marietta Corporation | Oxide coated metal grid electrode structure in display devices |
US5122925A (en) | 1991-04-22 | 1992-06-16 | Control Products, Inc. | Package for electronic components |
JP3118015B2 (en) | 1991-05-17 | 2000-12-18 | アークレイ株式会社 | Biosensor and separation and quantification method using the same |
US5209229A (en) | 1991-05-20 | 1993-05-11 | Telectronics Pacing Systems, Inc. | Apparatus and method employing plural electrode configurations for cardioversion of atrial fibrillation in an arrhythmia control system |
FI88223C (en) | 1991-05-22 | 1993-04-13 | Polar Electro Oy | Telemetric transmitter unit |
US5289497A (en) * | 1991-05-23 | 1994-02-22 | Interdigital Technology Corporation | Broadcast synchronized communication system |
JP2816262B2 (en) | 1991-07-09 | 1998-10-27 | 工業技術院長 | Carbon microsensor electrode and method of manufacturing the same |
DE4123348A1 (en) | 1991-07-15 | 1993-01-21 | Boehringer Mannheim Gmbh | ELECTROCHEMICAL ANALYSIS SYSTEM |
JP2740587B2 (en) | 1991-07-18 | 1998-04-15 | 工業技術院長 | Micro composite electrode and method of manufacturing the same |
CA2074702C (en) | 1991-07-29 | 1996-11-19 | Donald J. Urbas | Programmable transponder |
US5284156A (en) | 1991-08-30 | 1994-02-08 | M3 Systems, Inc. | Automatic tissue sampling apparatus |
GB9120144D0 (en) | 1991-09-20 | 1991-11-06 | Imperial College | A dialysis electrode device |
US5322063A (en) | 1991-10-04 | 1994-06-21 | Eli Lilly And Company | Hydrophilic polyurethane membranes for electrochemical glucose sensors |
US5264103A (en) | 1991-10-18 | 1993-11-23 | Matsushita Electric Industrial Co., Ltd. | Biosensor and a method for measuring a concentration of a substrate in a sample |
DE9113046U1 (en) | 1991-10-19 | 1991-12-19 | Frese, Volker, 7100 Heilbronn, De | |
US5236143A (en) | 1991-10-23 | 1993-08-17 | Dragon Bradley P | Intravenous tubing retractor apparatus |
US5217595A (en) | 1991-10-25 | 1993-06-08 | The Yellow Springs Instrument Company, Inc. | Electrochemical gas sensor |
US5415164A (en) | 1991-11-04 | 1995-05-16 | Biofield Corp. | Apparatus and method for screening and diagnosing trauma or disease in body tissues |
US5193539A (en) | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Implantable microstimulator |
US5358514A (en) | 1991-12-18 | 1994-10-25 | Alfred E. Mann Foundation For Scientific Research | Implantable microdevice with self-attaching electrodes |
US5193540A (en) | 1991-12-18 | 1993-03-16 | Alfred E. Mann Foundation For Scientific Research | Structure and method of manufacture of an implantable microstimulator |
US5372427A (en) | 1991-12-19 | 1994-12-13 | Texas Instruments Incorporated | Temperature sensor |
US5271815A (en) | 1991-12-26 | 1993-12-21 | Via Medical Corporation | Method for measuring glucose |
AU3274693A (en) | 1991-12-31 | 1993-07-28 | Abbott Laboratories | Composite membrane |
US5285792A (en) | 1992-01-10 | 1994-02-15 | Physio-Control Corporation | System for producing prioritized alarm messages in a medical instrument |
US5246867A (en) | 1992-01-17 | 1993-09-21 | University Of Maryland At Baltimore | Determination and quantification of saccharides by luminescence lifetimes and energy transfer |
NL9200207A (en) | 1992-02-05 | 1993-09-01 | Nedap Nv | IMPLANTABLE BIOMEDICAL SENSOR DEVICE, IN PARTICULAR FOR MEASUREMENT OF THE GLUCOSE CONCENTRATION. |
JP3144030B2 (en) | 1992-02-24 | 2001-03-07 | 東陶機器株式会社 | Health management network system |
US5431691A (en) | 1992-03-02 | 1995-07-11 | Siemens Pacesetter, Inc. | Method and system for recording and displaying a sequential series of pacing events |
US5309919A (en) | 1992-03-02 | 1994-05-10 | Siemens Pacesetter, Inc. | Method and system for recording, reporting, and displaying the distribution of pacing events over time and for using same to optimize programming |
US5328927A (en) | 1992-03-03 | 1994-07-12 | Merck Sharpe & Dohme, Ltd. | Hetercyclic compounds, processes for their preparation and pharmaceutical compositions containing them |
ZA931077B (en) | 1992-03-05 | 1994-01-04 | Qualcomm Inc | Apparatus and method for reducing message collision between mobile stations simultaneously accessing a base station in a cdma cellular communications system |
DE69319771T2 (en) | 1992-03-31 | 1999-04-22 | Dainippon Printing Co Ltd | Immobilized enzyme electrode, composition for its production and electrically conductive enzymes |
EP0636009B1 (en) | 1992-04-03 | 2000-11-29 | Micromedical Industries Limited | system for physiological monitoring |
FR2690622B1 (en) | 1992-04-29 | 1995-01-20 | Chronotec | Programmable ambulatory infusion pump system. |
US5711001A (en) | 1992-05-08 | 1998-01-20 | Motorola, Inc. | Method and circuit for acquisition by a radio receiver |
US5227042A (en) | 1992-05-15 | 1993-07-13 | The United States Of America As Represented By The United States Department Of Energy | Catalyzed enzyme electrodes |
US5580527A (en) | 1992-05-18 | 1996-12-03 | Moltech Corporation | Polymeric luminophores for sensing of oxygen |
US5269212A (en) | 1992-05-26 | 1993-12-14 | The Fletcher-Terry Company | Mat cutter |
GB9211402D0 (en) | 1992-05-29 | 1992-07-15 | Univ Manchester | Sensor devices |
US5333615A (en) | 1992-06-22 | 1994-08-02 | William Craelius | Apparatus for digitally recording and analyzing electrocardial and other bioelectric signals |
US5337258A (en) | 1992-07-10 | 1994-08-09 | Microsoft Corporation | Cost metrics |
DK95792A (en) | 1992-07-24 | 1994-01-25 | Radiometer As | Sensor for non-invasive, in vivo determination of an analyte and blood flow |
GB9217864D0 (en) | 1992-08-21 | 1992-10-07 | Unilever Plc | Monitoring method |
US5278079A (en) | 1992-09-02 | 1994-01-11 | Enzymatics, Inc. | Sealing device and method for inhibition of flow in capillary measuring devices |
CA2079192C (en) | 1992-09-25 | 1995-12-26 | Bernard Strong | Combined lancet and multi-function cap and lancet injector for use therewith |
US5898025A (en) | 1992-09-25 | 1999-04-27 | Henkel Kommanditgesellschaft Auf Aktien | Mildly alkaline dishwashing detergents |
US5376070A (en) | 1992-09-29 | 1994-12-27 | Minimed Inc. | Data transfer system for an infusion pump |
US5400782A (en) | 1992-10-07 | 1995-03-28 | Graphic Controls Corporation | Integral medical electrode including a fusible conductive substrate |
US5421816A (en) | 1992-10-14 | 1995-06-06 | Endodermic Medical Technologies Company | Ultrasonic transdermal drug delivery system |
US5387327A (en) | 1992-10-19 | 1995-02-07 | Duquesne University Of The Holy Ghost | Implantable non-enzymatic electrochemical glucose sensor |
US5320098A (en) | 1992-10-20 | 1994-06-14 | Sun Microsystems, Inc. | Optical transdermal link |
WO1994010553A1 (en) | 1992-10-23 | 1994-05-11 | Optex Biomedical, Inc. | Fibre-optic probe for the measurement of fluid parameters |
DE69331664T2 (en) | 1992-11-09 | 2002-10-17 | Ilife Systems Inc | DEVICE AND METHOD FOR REMOTELY MEASURING PHYSIOLOGICAL SIZES |
US5832448A (en) | 1996-10-16 | 1998-11-03 | Health Hero Network | Multiple patient monitoring system for proactive health management |
US6330426B2 (en) | 1994-05-23 | 2001-12-11 | Stephen J. Brown | System and method for remote education using a memory card |
US6968375B1 (en) | 1997-03-28 | 2005-11-22 | Health Hero Network, Inc. | Networked system for interactive communication and remote monitoring of individuals |
US5960403A (en) | 1992-11-17 | 1999-09-28 | Health Hero Network | Health management process control system |
US5940801A (en) | 1994-04-26 | 1999-08-17 | Health Hero Network, Inc. | Modular microprocessor-based diagnostic measurement apparatus and method for psychological conditions |
US5879163A (en) | 1996-06-24 | 1999-03-09 | Health Hero Network, Inc. | On-line health education and feedback system using motivational driver profile coding and automated content fulfillment |
US5897493A (en) | 1997-03-28 | 1999-04-27 | Health Hero Network, Inc. | Monitoring system for remotely querying individuals |
US5956501A (en) | 1997-01-10 | 1999-09-21 | Health Hero Network, Inc. | Disease simulation system and method |
US5678571A (en) | 1994-05-23 | 1997-10-21 | Raya Systems, Inc. | Method for treating medical conditions using a microprocessor-based video game |
US6210272B1 (en) | 1997-12-22 | 2001-04-03 | Health Hero Network, Inc. | Multi-player interactive electronic game for health education |
US5913310A (en) | 1994-05-23 | 1999-06-22 | Health Hero Network, Inc. | Method for diagnosis and treatment of psychological and emotional disorders using a microprocessor-based video game |
US5933136A (en) | 1996-12-23 | 1999-08-03 | Health Hero Network, Inc. | Network media access control system for encouraging patient compliance with a treatment plan |
US6101478A (en) | 1997-04-30 | 2000-08-08 | Health Hero Network | Multi-user remote health monitoring system |
US6196970B1 (en) | 1999-03-22 | 2001-03-06 | Stephen J. Brown | Research data collection and analysis |
US5887133A (en) | 1997-01-15 | 1999-03-23 | Health Hero Network | System and method for modifying documents sent over a communications network |
US5307263A (en) | 1992-11-17 | 1994-04-26 | Raya Systems, Inc. | Modular microprocessor-based health monitoring system |
US20030212579A1 (en) | 2002-05-08 | 2003-11-13 | Brown Stephen J. | Remote health management system |
US5899855A (en) | 1992-11-17 | 1999-05-04 | Health Hero Network, Inc. | Modular microprocessor-based health monitoring system |
US5782814A (en) | 1994-07-22 | 1998-07-21 | Raya Systems, Inc. | Apparatus for determining and recording injection doses in syringes using electrical inductance |
US5997476A (en) | 1997-03-28 | 1999-12-07 | Health Hero Network, Inc. | Networked system for interactive communication and remote monitoring of individuals |
US7970620B2 (en) | 1992-11-17 | 2011-06-28 | Health Hero Network, Inc. | Multi-user remote health monitoring system with biometrics support |
US6068615A (en) | 1994-07-22 | 2000-05-30 | Health Hero Network, Inc. | Inductance-based dose measurement in syringes |
US6334778B1 (en) | 1994-04-26 | 2002-01-01 | Health Hero Network, Inc. | Remote psychological diagnosis and monitoring system |
US5601435A (en) | 1994-11-04 | 1997-02-11 | Intercare | Method and apparatus for interactively monitoring a physiological condition and for interactively providing health related information |
US5951300A (en) | 1997-03-10 | 1999-09-14 | Health Hero Network | Online system and method for providing composite entertainment and health information |
US5569212A (en) | 1994-07-22 | 1996-10-29 | Raya Systems, Inc. | Apparatus for electrically determining injection doses in syringes |
US20010011224A1 (en) | 1995-06-07 | 2001-08-02 | Stephen James Brown | Modular microprocessor-based health monitoring system |
US6168563B1 (en) | 1992-11-17 | 2001-01-02 | Health Hero Network, Inc. | Remote health monitoring and maintenance system |
US5918603A (en) | 1994-05-23 | 1999-07-06 | Health Hero Network, Inc. | Method for treating medical conditions using a microprocessor-based video game |
US6186145B1 (en) | 1994-05-23 | 2001-02-13 | Health Hero Network, Inc. | Method for diagnosis and treatment of psychological and emotional conditions using a microprocessor-based virtual reality simulator |
US5371687A (en) | 1992-11-20 | 1994-12-06 | Boehringer Mannheim Corporation | Glucose test data acquisition and management system |
ZA938555B (en) | 1992-11-23 | 1994-08-02 | Lilly Co Eli | Technique to improve the performance of electrochemical sensors |
US5410326A (en) | 1992-12-04 | 1995-04-25 | Goldstein; Steven W. | Programmable remote control device for interacting with a plurality of remotely controlled devices |
US5379764A (en) | 1992-12-09 | 1995-01-10 | Diasense, Inc. | Non-invasive determination of analyte concentration in body of mammals |
DK148592D0 (en) | 1992-12-10 | 1992-12-10 | Novo Nordisk As | APPARATUS |
US5358135A (en) | 1992-12-28 | 1994-10-25 | Square D Company | Access door hinge attachment |
US5342408A (en) | 1993-01-07 | 1994-08-30 | Incontrol, Inc. | Telemetry system for an implantable cardiac device |
US5299571A (en) | 1993-01-22 | 1994-04-05 | Eli Lilly And Company | Apparatus and method for implantation of sensors |
US5499243A (en) * | 1993-01-22 | 1996-03-12 | Hall; Dennis R. | Method and apparatus for coordinating transfer of information between a base station and a plurality of radios |
US5371734A (en) | 1993-01-29 | 1994-12-06 | Digital Ocean, Inc. | Medium access control protocol for wireless network |
FR2701117B1 (en) | 1993-02-04 | 1995-03-10 | Asulab Sa | Electrochemical measurement system with multizone sensor, and its application to glucose measurement. |
JPH0816669B2 (en) | 1993-02-18 | 1996-02-21 | 日本電気株式会社 | Method for manufacturing glucose sensor |
US5371787A (en) | 1993-03-01 | 1994-12-06 | Dialogic Corporation | Machine answer detection |
GB9304306D0 (en) | 1993-03-03 | 1993-04-21 | Univ Alberta | Glucose sensor |
US5600301A (en) * | 1993-03-11 | 1997-02-04 | Schrader Automotive Inc. | Remote tire pressure monitoring system employing coded tire identification and radio frequency transmission, and enabling recalibration upon tire rotation or replacement |
US5433710A (en) | 1993-03-16 | 1995-07-18 | Minimed, Inc. | Medication infusion pump with fluoropolymer valve seat |
US5257971A (en) | 1993-03-16 | 1993-11-02 | Minimed Technologies, Ltd. | Recondition process for a medication infusion pump |
US5400794A (en) * | 1993-03-19 | 1995-03-28 | Gorman; Peter G. | Biomedical response monitor and technique using error correction |
US5257980A (en) | 1993-04-05 | 1993-11-02 | Minimed Technologies, Ltd. | Subcutaneous injection set with crimp-free soft cannula |
US5793292A (en) | 1993-04-22 | 1998-08-11 | Ivey, Jr.; Ellwood G. | System for inhibiting use of a hand-operated machine by an impaired individual through detection of toxins in the individual |
GB9309797D0 (en) | 1993-05-12 | 1993-06-23 | Medisense Inc | Electrochemical sensors |
US5364797A (en) | 1993-05-20 | 1994-11-15 | Mobil Oil Corp. | Sensor device containing mesoporous crystalline material |
JP3713516B2 (en) | 1993-05-29 | 2005-11-09 | ケンブリッジ ライフ サイエンシズ パブリック リミテッド カンパニー | Sensors based on polymer transformations |
DE4318519C2 (en) | 1993-06-03 | 1996-11-28 | Fraunhofer Ges Forschung | Electrochemical sensor |
CA2153883C (en) | 1993-06-08 | 1999-02-09 | Bradley E. White | Biosensing meter which detects proper electrode engagement and distinguishes sample and check strips |
US5366609A (en) | 1993-06-08 | 1994-11-22 | Boehringer Mannheim Corporation | Biosensing meter with pluggable memory key |
DE4320463A1 (en) | 1993-06-21 | 1994-12-22 | Boehringer Mannheim Gmbh | Blood lancet device for drawing blood for diagnostic purposes |
US5477855A (en) | 1993-07-16 | 1995-12-26 | Alfred E. Mann Foundation For Scientific Research | Shield for conductors of an implantable device |
US5413690A (en) | 1993-07-23 | 1995-05-09 | Boehringer Mannheim Corporation | Potentiometric biosensor and the method of its use |
US5410474A (en) | 1993-07-27 | 1995-04-25 | Miles Inc. | Buttonless memory system for an electronic measurement device |
JP2979933B2 (en) | 1993-08-03 | 1999-11-22 | セイコーエプソン株式会社 | Pulse wave analyzer |
CA2170402C (en) | 1993-08-24 | 2000-07-18 | Michael P. Allen | Novel disposable electronic assay device |
US5837546A (en) | 1993-08-24 | 1998-11-17 | Metrika, Inc. | Electronic assay device and method |
CA2174719C (en) | 1993-08-24 | 2005-07-26 | Mark R. Robinson | A robust accurate non-invasive analyte monitor |
US5377258A (en) | 1993-08-30 | 1994-12-27 | National Medical Research Council | Method and apparatus for an automated and interactive behavioral guidance system |
US5456692A (en) | 1993-09-03 | 1995-10-10 | Pacesetter, Inc. | System and method for noninvasively altering the function of an implanted pacemaker |
DE4329898A1 (en) | 1993-09-04 | 1995-04-06 | Marcus Dr Besson | Wireless medical diagnostic and monitoring device |
US5438983A (en) | 1993-09-13 | 1995-08-08 | Hewlett-Packard Company | Patient alarm detection using trend vector analysis |
EP0644266A1 (en) | 1993-09-22 | 1995-03-22 | Siemens Aktiengesellschaft | Working electrode for electrochemical-enzymatical sensor systems |
US5582184A (en) | 1993-10-13 | 1996-12-10 | Integ Incorporated | Interstitial fluid collection and constituent measurement |
DE69322968T2 (en) | 1993-10-22 | 1999-07-08 | Siemens Elema Ab | Method and device for continuously monitoring an anolyte level |
US5399823A (en) | 1993-11-10 | 1995-03-21 | Minimed Inc. | Membrane dome switch with tactile feel regulator shim |
US5458140A (en) | 1993-11-15 | 1995-10-17 | Non-Invasive Monitoring Company (Nimco) | Enhancement of transdermal monitoring applications with ultrasound and chemical enhancers |
US20020169394A1 (en) | 1993-11-15 | 2002-11-14 | Eppstein Jonathan A. | Integrated tissue poration, fluid harvesting and analysis device, and method therefor |
US5814599A (en) | 1995-08-04 | 1998-09-29 | Massachusetts Insitiute Of Technology | Transdermal delivery of encapsulated drugs |
US5885211A (en) | 1993-11-15 | 1999-03-23 | Spectrix, Inc. | Microporation of human skin for monitoring the concentration of an analyte |
US5445611A (en) | 1993-12-08 | 1995-08-29 | Non-Invasive Monitoring Company (Nimco) | Enhancement of transdermal delivery with ultrasound and chemical enhancers |
DE4339188A1 (en) | 1993-11-16 | 1995-05-18 | Mueller & Sebastiani Elek Gmbh | Portable device for recording body-specific measurement data |
US5497772A (en) | 1993-11-19 | 1996-03-12 | Alfred E. Mann Foundation For Scientific Research | Glucose monitoring system |
US5791344A (en) | 1993-11-19 | 1998-08-11 | Alfred E. Mann Foundation For Scientific Research | Patient monitoring system |
CA2155932A1 (en) | 1993-12-14 | 1995-06-22 | Tadakazu Yamauchi | Medical measuring apparatus |
US5724968A (en) | 1993-12-29 | 1998-03-10 | First Opinion Corporation | Computerized medical diagnostic system including meta function |
US6206829B1 (en) | 1996-07-12 | 2001-03-27 | First Opinion Corporation | Computerized medical diagnostic and treatment advice system including network access |
US5589326A (en) | 1993-12-30 | 1996-12-31 | Boehringer Mannheim Corporation | Osmium-containing redox mediator |
DE4401400A1 (en) | 1994-01-19 | 1995-07-20 | Ernst Prof Dr Pfeiffer | Method and arrangement for continuously monitoring the concentration of a metabolite |
FR2715566B1 (en) | 1994-02-03 | 1996-03-08 | Synthelabo | Concentrated aqueous solutions of argatroban. |
EP0752099A1 (en) | 1994-02-09 | 1997-01-08 | Abbott Laboratories | Diagnostic flow cell device |
FI95574C (en) | 1994-02-16 | 1996-02-26 | Valtion Teknillinen | Electron-conducting molecular preparations |
US5437999A (en) | 1994-02-22 | 1995-08-01 | Boehringer Mannheim Corporation | Electrochemical sensor |
US5536249A (en) | 1994-03-09 | 1996-07-16 | Visionary Medical Products, Inc. | Pen-type injector with a microprocessor and blood characteristic monitor |
DE4408718A1 (en) | 1994-03-15 | 1995-09-21 | Henkel Kgaa | Breakage and storage stable, polyfunctional cleaning tablets, process for their preparation and their use |
US5390671A (en) | 1994-03-15 | 1995-02-21 | Minimed Inc. | Transcutaneous sensor insertion set |
US5391250A (en) | 1994-03-15 | 1995-02-21 | Minimed Inc. | Method of fabricating thin film sensors |
US5456940A (en) | 1994-03-28 | 1995-10-10 | Minimed Inc. | System for lubricating a syringe barrel |
US5527307A (en) | 1994-04-01 | 1996-06-18 | Minimed Inc. | Implantable medication infusion pump with discharge side port |
US5505713A (en) | 1994-04-01 | 1996-04-09 | Minimed Inc. | Indwelling catheter with stable enzyme coating |
AU2200895A (en) | 1994-04-04 | 1995-10-23 | Motorola, Inc. | Method and apparatus for activating and accessing remote meter interface devices |
US5609575A (en) | 1994-04-11 | 1997-03-11 | Graseby Medical Limited | Infusion pump and method with dose-rate calculation |
JP3061351B2 (en) | 1994-04-25 | 2000-07-10 | 松下電器産業株式会社 | Method and apparatus for quantifying specific compounds |
US5569186A (en) | 1994-04-25 | 1996-10-29 | Minimed Inc. | Closed loop infusion pump system with removable glucose sensor |
EP0760138A4 (en) | 1994-04-26 | 1998-04-01 | Raya Systems Inc | Modular microprocessor-based diagnostic measurement system for psychological conditions |
US5370622A (en) | 1994-04-28 | 1994-12-06 | Minimed Inc. | Proctective case for a medication infusion pump |
US5476460A (en) | 1994-04-29 | 1995-12-19 | Minimed Inc. | Implantable infusion port with reduced internal volume |
EP0758377A1 (en) | 1994-05-03 | 1997-02-19 | Novo Nordisk A/S | Alkaline glucose oxidase |
DE4415896A1 (en) | 1994-05-05 | 1995-11-09 | Boehringer Mannheim Gmbh | Analysis system for monitoring the concentration of an analyte in the blood of a patient |
TW275570B (en) | 1994-05-05 | 1996-05-11 | Boehringer Mannheim Gmbh | |
US5651767A (en) | 1994-05-06 | 1997-07-29 | Alfred F. Mann Foundation For Scientific Research | Replaceable catheter system for physiological sensors, stimulating electrodes and/or implantable fluid delivery systems |
US5484404A (en) | 1994-05-06 | 1996-01-16 | Alfred E. Mann Foundation For Scientific Research | Replaceable catheter system for physiological sensors, tissue stimulating electrodes and/or implantable fluid delivery systems |
US5545191A (en) | 1994-05-06 | 1996-08-13 | Alfred E. Mann Foundation For Scientific Research | Method for optimally positioning and securing the external unit of a transcutaneous transducer of the skin of a living body |
US5482473A (en) | 1994-05-09 | 1996-01-09 | Minimed Inc. | Flex circuit connector |
JP3027306B2 (en) | 1994-06-02 | 2000-04-04 | 松下電器産業株式会社 | Biosensor and manufacturing method thereof |
US5472317A (en) | 1994-06-03 | 1995-12-05 | Minimed Inc. | Mounting clip for a medication infusion pump |
US5514103A (en) | 1994-06-14 | 1996-05-07 | Minimed Inc. | Medication infusion pump with improved pressure reservoir |
US5462525A (en) | 1994-06-14 | 1995-10-31 | Minimed, Inc., A Delaware Corporation | Flow sensor for an infusion pump |
US5460618A (en) | 1994-06-20 | 1995-10-24 | Minimed Inc. | Side slit catheter |
US5771890A (en) | 1994-06-24 | 1998-06-30 | Cygnus, Inc. | Device and method for sampling of substances using alternating polarity |
US5494562A (en) | 1994-06-27 | 1996-02-27 | Ciba Corning Diagnostics Corp. | Electrochemical sensors |
US5809417A (en) | 1994-07-05 | 1998-09-15 | Lucent Technologies Inc. | Cordless telephone arranged for operating with multiple portable units in a frequency hopping system |
US5514253A (en) | 1994-07-13 | 1996-05-07 | I-Stat Corporation | Method of measuring gas concentrations and microfabricated sensing device for practicing same |
US5605152A (en) | 1994-07-18 | 1997-02-25 | Minimed Inc. | Optical glucose sensor |
US6110148A (en) | 1994-07-22 | 2000-08-29 | Health Hero Network, Inc. | Capacitance-based dose measurements in syringes |
US5792117A (en) | 1994-07-22 | 1998-08-11 | Raya Systems, Inc. | Apparatus for optically determining and electronically recording injection doses in syringes |
US5720733A (en) | 1994-07-22 | 1998-02-24 | Raya Systems, Inc. | Apparatus for determining and recording injection doses in syringes using electrical capacitance measurements |
US5629981A (en) | 1994-07-29 | 1997-05-13 | Texas Instruments Incorporated | Information management and security system |
US5518006A (en) | 1994-08-09 | 1996-05-21 | International Technidyne Corp. | Blood sampling device |
DE4430023A1 (en) | 1994-08-24 | 1996-02-29 | Boehringer Mannheim Gmbh | Electrochemical sensor |
US5462051A (en) | 1994-08-31 | 1995-10-31 | Colin Corporation | Medical communication system |
WO1996007908A1 (en) | 1994-09-08 | 1996-03-14 | Lifescan, Inc. | Optically readable strip for analyte detection having on-strip standard |
US5526120A (en) | 1994-09-08 | 1996-06-11 | Lifescan, Inc. | Test strip with an asymmetrical end insuring correct insertion for measuring |
US5505709A (en) | 1994-09-15 | 1996-04-09 | Minimed, Inc., A Delaware Corporation | Mated infusion pump and syringe |
US5549115A (en) | 1994-09-28 | 1996-08-27 | Heartstream, Inc. | Method and apparatus for gathering event data using a removable data storage medium and clock |
US5724030A (en) * | 1994-10-13 | 1998-03-03 | Bio Medic Data Systems, Inc. | System monitoring reprogrammable implantable transponder |
US5667983A (en) | 1994-10-24 | 1997-09-16 | Chiron Diagnostics Corporation | Reagents with enhanced performance in clinical diagnostic systems |
US5545152A (en) | 1994-10-28 | 1996-08-13 | Minimed Inc. | Quick-connect coupling for a medication infusion system |
IE72524B1 (en) | 1994-11-04 | 1997-04-23 | Elan Med Tech | Analyte-controlled liquid delivery device and analyte monitor |
US5487751A (en) | 1994-11-04 | 1996-01-30 | Physio-Control Corporation | Mechanical connector for securing compatible medical instruments together |
US6256643B1 (en) | 1998-03-10 | 2001-07-03 | Baxter International Inc. | Systems and methods for storing, retrieving, and manipulating data in medical processing devices |
US5919141A (en) | 1994-11-15 | 1999-07-06 | Life Sensing Instrument Company, Inc. | Vital sign remote monitoring device |
US5637095A (en) | 1995-01-13 | 1997-06-10 | Minimed Inc. | Medication infusion pump with flexible drive plunger |
US5562713A (en) | 1995-01-18 | 1996-10-08 | Pacesetter, Inc. | Bidirectional telemetry apparatus and method for implantable device |
EP0724859B1 (en) | 1995-02-04 | 1997-11-12 | Baumann & Haldi S.A. | Personal device for measurement, processing and transmission of substantially physiological data |
US6153069A (en) | 1995-02-09 | 2000-11-28 | Tall Oak Ventures | Apparatus for amperometric Diagnostic analysis |
US6515593B1 (en) | 1995-02-15 | 2003-02-04 | Izex Technologies, Inc. | Communication system for an instrumented orthopedic restraining device and method therefor |
US5568806A (en) | 1995-02-16 | 1996-10-29 | Minimed Inc. | Transcutaneous sensor insertion set |
US5586553A (en) | 1995-02-16 | 1996-12-24 | Minimed Inc. | Transcutaneous sensor insertion set |
US5651869A (en) | 1995-02-28 | 1997-07-29 | Matsushita Electric Industrial Co., Ltd. | Biosensor |
US5647853A (en) | 1995-03-03 | 1997-07-15 | Minimed Inc. | Rapid response occlusion detector for a medication infusion pump |
US5596150A (en) | 1995-03-08 | 1997-01-21 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Capacitance probe for fluid flow and volume measurements |
US6066448A (en) | 1995-03-10 | 2000-05-23 | Meso Sclae Technologies, Llc. | Multi-array, multi-specific electrochemiluminescence testing |
JPH08247987A (en) | 1995-03-15 | 1996-09-27 | Omron Corp | Portable measuring instrument |
US5650062A (en) | 1995-03-17 | 1997-07-22 | Matsushita Electric Industrial Co., Ltd. | Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same |
US5582697A (en) | 1995-03-17 | 1996-12-10 | Matsushita Electric Industrial Co., Ltd. | Biosensor, and a method and a device for quantifying a substrate in a sample liquid using the same |
US5882494A (en) | 1995-03-27 | 1999-03-16 | Minimed, Inc. | Polyurethane/polyurea compositions containing silicone for biosensor membranes |
US5786439A (en) | 1996-10-24 | 1998-07-28 | Minimed Inc. | Hydrophilic, swellable coatings for biosensors |
US6170318B1 (en) | 1995-03-27 | 2001-01-09 | California Institute Of Technology | Methods of use for sensor based fluid detection devices |
US5695949A (en) | 1995-04-07 | 1997-12-09 | Lxn Corp. | Combined assay for current glucose level and intermediate or long-term glycemic control |
JP3498105B2 (en) | 1995-04-07 | 2004-02-16 | アークレイ株式会社 | Sensor, method for manufacturing the same, and measuring method using the sensor |
DE19515524C2 (en) | 1995-04-27 | 1999-09-09 | Private Uni Witten Herdecke Gm | Method and device for the continuous detection of at least one substance in a gaseous or liquid mixture by means of a sensor electrode |
US5752512A (en) | 1995-05-10 | 1998-05-19 | Massachusetts Institute Of Technology | Apparatus and method for non-invasive blood analyte measurement |
US5876484A (en) | 1995-05-17 | 1999-03-02 | Phytotech, Inc. | Method for removing soluble metals from an aqueous phase |
US5628310A (en) | 1995-05-19 | 1997-05-13 | Joseph R. Lakowicz | Method and apparatus to perform trans-cutaneous analyte monitoring |
US5640764A (en) | 1995-05-22 | 1997-06-24 | Alfred E. Mann Foundation For Scientific Research | Method of forming a tubular feed-through hermetic seal for an implantable medical device |
US6035237A (en) | 1995-05-23 | 2000-03-07 | Alfred E. Mann Foundation | Implantable stimulator that prevents DC current flow without the use of discrete output coupling capacitors |
US5665065A (en) | 1995-05-26 | 1997-09-09 | Minimed Inc. | Medication infusion device with blood glucose data input |
US5615135A (en) | 1995-06-01 | 1997-03-25 | International Business Machines Corporation | Event driven interface having a dynamically reconfigurable counter for monitoring a high speed data network according to changing traffic events |
US5623925A (en) | 1995-06-05 | 1997-04-29 | Cmed, Inc. | Virtual medical instrument for performing medical diagnostic testing on patients |
US5721783A (en) | 1995-06-07 | 1998-02-24 | Anderson; James C. | Hearing aid with wireless remote processor |
US5584813A (en) | 1995-06-07 | 1996-12-17 | Minimed Inc. | Subcutaneous injection set |
US5567302A (en) | 1995-06-07 | 1996-10-22 | Molecular Devices Corporation | Electrochemical system for rapid detection of biochemical agents that catalyze a redox potential change |
US5995860A (en) | 1995-07-06 | 1999-11-30 | Thomas Jefferson University | Implantable sensor and system for measurement and control of blood constituent levels |
JP2819260B2 (en) | 1995-07-11 | 1998-10-30 | 株式会社朋友メディカル | Catheter extension tube |
US5611900A (en) | 1995-07-20 | 1997-03-18 | Michigan State University | Microbiosensor used in-situ |
US5947921A (en) | 1995-12-18 | 1999-09-07 | Massachusetts Institute Of Technology | Chemical and physical enhancers and ultrasound for transdermal drug delivery |
US6002961A (en) | 1995-07-25 | 1999-12-14 | Massachusetts Institute Of Technology | Transdermal protein delivery using low-frequency sonophoresis |
US6041253A (en) | 1995-12-18 | 2000-03-21 | Massachusetts Institute Of Technology | Effect of electric field and ultrasound for transdermal drug delivery |
US5750926A (en) | 1995-08-16 | 1998-05-12 | Alfred E. Mann Foundation For Scientific Research | Hermetically sealed electrical feedthrough for use with implantable electronic devices |
DE19530376C2 (en) | 1995-08-18 | 1999-09-02 | Fresenius Ag | Biosensor |
US5786584A (en) | 1995-09-06 | 1998-07-28 | Eli Lilly And Company | Vial and cartridge reading device providing audio feedback for a blood glucose monitoring system |
US5682233A (en) | 1995-09-08 | 1997-10-28 | Integ, Inc. | Interstitial fluid sampler |
US5989409A (en) | 1995-09-11 | 1999-11-23 | Cygnus, Inc. | Method for glucose sensing |
US5735273A (en) | 1995-09-12 | 1998-04-07 | Cygnus, Inc. | Chemical signal-impermeable mask |
US5628890A (en) | 1995-09-27 | 1997-05-13 | Medisense, Inc. | Electrochemical sensor |
US5972199A (en) | 1995-10-11 | 1999-10-26 | E. Heller & Company | Electrochemical analyte sensors using thermostable peroxidase |
US5665222A (en) | 1995-10-11 | 1997-09-09 | E. Heller & Company | Soybean peroxidase electrochemical sensor |
US5741211A (en) | 1995-10-26 | 1998-04-21 | Medtronic, Inc. | System and method for continuous monitoring of diabetes-related blood constituents |
US5701894A (en) | 1995-11-09 | 1997-12-30 | Del Mar Avionics | Modular physiological computer-recorder |
US5748103A (en) | 1995-11-13 | 1998-05-05 | Vitalcom, Inc. | Two-way TDMA telemetry system with power conservation features |
US5807315A (en) | 1995-11-13 | 1998-09-15 | Minimed, Inc. | Methods and devices for the delivery of monomeric proteins |
DE19543020A1 (en) | 1995-11-18 | 1997-05-22 | Boehringer Mannheim Gmbh | Method and device for determining analytical data on the interior of a scattering matrix |
US5711861A (en) | 1995-11-22 | 1998-01-27 | Ward; W. Kenneth | Device for monitoring changes in analyte concentration |
WO1997019188A1 (en) | 1995-11-22 | 1997-05-29 | Minimed, Inc. | Detection of biological molecules using chemical amplification and optical sensors |
US6002954A (en) | 1995-11-22 | 1999-12-14 | The Regents Of The University Of California | Detection of biological molecules using boronate-based chemical amplification and optical sensors |
US6766183B2 (en) | 1995-11-22 | 2004-07-20 | Medtronic Minimed, Inc. | Long wave fluorophore sensor compounds and other fluorescent sensor compounds in polymers |
US5981294A (en) | 1995-11-29 | 1999-11-09 | Metrika, Inc. | Device for blood separation in a diagnostic device |
US5730654A (en) | 1995-12-18 | 1998-03-24 | Raya Systems, Inc. | Multi-player video game for health education |
EP0868144B1 (en) | 1995-12-19 | 2005-01-26 | Abbott Laboratories | Device for the detection of analyte and administration of a therapeutic substance |
JP3316820B2 (en) | 1995-12-28 | 2002-08-19 | シィグナス インコーポレィティド | Apparatus and method for continuous monitoring of a physiological analyte of a subject |
US5827184A (en) | 1995-12-29 | 1998-10-27 | Minnesota Mining And Manufacturing Company | Self-packaging bioelectrodes |
JP3365184B2 (en) | 1996-01-10 | 2003-01-08 | 松下電器産業株式会社 | Biosensor |
US5830341A (en) | 1996-01-23 | 1998-11-03 | Gilmartin; Markas A. T. | Electrodes and metallo isoindole ringed compounds |
US5628309A (en) | 1996-01-25 | 1997-05-13 | Raya Systems, Inc. | Meter for electrically measuring and recording injection syringe doses |
US5704922A (en) | 1996-01-25 | 1998-01-06 | Raya Systems, Inc. | Syringe having electrical contact points for metering doses |
EP0889703B1 (en) | 1996-02-05 | 2001-11-21 | Diasense, Inc. | Apparatus for non-invasive glucose sensing |
FI118509B (en) | 1996-02-12 | 2007-12-14 | Nokia Oyj | A method and apparatus for predicting blood glucose levels in a patient |
FI960636A (en) | 1996-02-12 | 1997-08-13 | Nokia Mobile Phones Ltd | A procedure for monitoring the health of a patient |
US6241862B1 (en) | 1996-02-14 | 2001-06-05 | Inverness Medical Technology, Inc. | Disposable test strips with integrated reagent/blood separation layer |
US5708247A (en) | 1996-02-14 | 1998-01-13 | Selfcare, Inc. | Disposable glucose test strips, and methods and compositions for making same |
US5948512A (en) | 1996-02-22 | 1999-09-07 | Seiko Epson Corporation | Ink jet recording ink and recording method |
US20010044588A1 (en) | 1996-02-22 | 2001-11-22 | Mault James R. | Monitoring system |
US5833603A (en) | 1996-03-13 | 1998-11-10 | Lipomatrix, Inc. | Implantable biosensing transponder |
US5753452A (en) | 1996-04-04 | 1998-05-19 | Lifescan, Inc. | Reagent test strip for blood glucose determination |
FR2748171B1 (en) | 1996-04-30 | 1998-07-17 | Motorola Inc | METHOD FOR GENERATING A CLOCK SIGNAL FOR USE IN A DATA RECEIVER, CLOCK GENERATOR, DATA RECEIVER AND REMOTE CONTROL ACCESS SYSTEM FOR VEHICLES |
CA2250400A1 (en) | 1996-04-30 | 1997-11-06 | Metrika, Inc. | Method and device for measuring reflected optical radiation |
DE19618597B4 (en) | 1996-05-09 | 2005-07-21 | Institut für Diabetestechnologie Gemeinnützige Forschungs- und Entwicklungsgesellschaft mbH an der Universität Ulm | Method for determining the concentration of tissue glucose |
US6130602A (en) | 1996-05-13 | 2000-10-10 | Micron Technology, Inc. | Radio frequency data communications device |
US5968839A (en) | 1996-05-13 | 1999-10-19 | Metrika, Inc. | Method and device producing a predetermined distribution of detectable change in assays |
JP3494660B2 (en) | 1996-05-17 | 2004-02-09 | アミラ メディカル | A device that squeezes body fluid from the incision |
AU3070397A (en) | 1996-05-17 | 1997-12-05 | Mercury Diagnostics Inc. | Methods and apparatus for sampling body fluid |
EP0906062B1 (en) | 1996-05-17 | 2007-12-26 | Roche Diagnostics Operations, Inc. | Body fluid sampling device |
US5857983A (en) | 1996-05-17 | 1999-01-12 | Mercury Diagnostics, Inc. | Methods and apparatus for sampling body fluid |
US5951492A (en) | 1996-05-17 | 1999-09-14 | Mercury Diagnostics, Inc. | Methods and apparatus for sampling and analyzing body fluid |
US5879311A (en) | 1996-05-17 | 1999-03-09 | Mercury Diagnostics, Inc. | Body fluid sampling device and methods of use |
US5954685A (en) | 1996-05-24 | 1999-09-21 | Cygnus, Inc. | Electrochemical sensor with dual purpose electrode |
US5735285A (en) | 1996-06-04 | 1998-04-07 | Data Critical Corp. | Method and hand-held apparatus for demodulating and viewing frequency modulated biomedical signals |
EP0914178B1 (en) | 1996-06-18 | 2003-03-12 | Alza Corporation | Device for enhancing transdermal agent delivery or sampling |
US5830064A (en) | 1996-06-21 | 1998-11-03 | Pear, Inc. | Apparatus and method for distinguishing events which collectively exceed chance expectations and thereby controlling an output |
US6032199A (en) | 1996-06-26 | 2000-02-29 | Sun Microsystems, Inc. | Transport independent invocation and servant interfaces that permit both typecode interpreted and compiled marshaling |
JP3581218B2 (en) | 1996-07-03 | 2004-10-27 | 株式会社東芝 | Mobile communication terminal device and its mobile phone and data terminal device |
CA2259254C (en) | 1996-07-08 | 2008-02-19 | Animas Corporation | Implantable sensor and system for in vivo measurement and control of fluid constituent levels |
US5707502A (en) | 1996-07-12 | 1998-01-13 | Chiron Diagnostics Corporation | Sensors for measuring analyte concentrations and methods of making same |
US5781024A (en) | 1996-07-26 | 1998-07-14 | Diametrics Medical, Inc. | Instrument performance verification system |
US5733313A (en) | 1996-08-01 | 1998-03-31 | Exonix Corporation | RF coupled, implantable medical device with rechargeable back-up power source |
US6741163B1 (en) | 1996-08-13 | 2004-05-25 | Corinna A. Roberts | Decorative motion detector |
US5804048A (en) | 1996-08-15 | 1998-09-08 | Via Medical Corporation | Electrode assembly for assaying glucose |
US5945345A (en) | 1996-08-27 | 1999-08-31 | Metrika, Inc. | Device for preventing assay interference using silver or lead to remove the interferant |
FI112029B (en) | 1996-09-02 | 2003-10-31 | Nokia Corp | Device for taking and analyzing samples in liquid form, such as blood samples |
US6544193B2 (en) | 1996-09-04 | 2003-04-08 | Marcio Marc Abreu | Noninvasive measurement of chemical substances |
US5869963A (en) | 1996-09-12 | 1999-02-09 | Alps Electric Co., Ltd. | Magnetoresistive sensor and head |
US5729225A (en) | 1996-09-23 | 1998-03-17 | Motorola, Inc. | Method and apparatus for asynchronous digital mixing |
DK0929644T3 (en) | 1996-09-24 | 2002-05-21 | Henkel Ecolab Gmbh & Co Ohg | Manufacture of surfactant-containing, compact detergent |
US5718234A (en) | 1996-09-30 | 1998-02-17 | Northrop Grumman Corporation | Physiological data communication system |
US6148094A (en) | 1996-09-30 | 2000-11-14 | David J. Kinsella | Pointing device with biometric sensor |
US5769873A (en) | 1996-10-15 | 1998-06-23 | Pacesetter, Inc. | Meter for measuring battery charge delivered in an implantable device |
US5977476A (en) | 1996-10-16 | 1999-11-02 | United Solar Systems Corporation | High efficiency photovoltaic device |
EP2290362B1 (en) | 1996-10-30 | 2013-01-23 | F. Hoffmann-La Roche AG | Synchronized analyte testing system |
US6443942B2 (en) | 1996-11-01 | 2002-09-03 | Minimed, Inc. | Medication device with protein stabilizing surface coating |
US5854078A (en) | 1996-11-06 | 1998-12-29 | University Of Pittsburgh | Polymerized crystalline colloidal array sensor methods |
US5771001A (en) | 1996-11-18 | 1998-06-23 | Cobb; Marlon J. | Personal alarm system |
US5856758A (en) * | 1996-11-20 | 1999-01-05 | Adtran, Inc. | Low distortion driver employing positive feedback for reducing power loss in output impedance that effectively matches the impedance of driven line |
WO1998022820A1 (en) | 1996-11-21 | 1998-05-28 | Lawrence Livermore National Laboratory | Detection of biological molecules using boronate-based chemical amplification and optical sensors |
US6027459A (en) | 1996-12-06 | 2000-02-22 | Abbott Laboratories | Method and apparatus for obtaining blood for diagnostic tests |
US5964993A (en) | 1996-12-19 | 1999-10-12 | Implanted Biosystems Inc. | Glucose sensor |
US6043437A (en) | 1996-12-20 | 2000-03-28 | Alfred E. Mann Foundation | Alumina insulation for coating implantable components and other microminiature devices |
US6151586A (en) | 1996-12-23 | 2000-11-21 | Health Hero Network, Inc. | Computerized reward system for encouraging participation in a health management program |
US6130623A (en) | 1996-12-31 | 2000-10-10 | Lucent Technologies Inc. | Encryption for modulated backscatter systems |
GB9700090D0 (en) | 1997-01-04 | 1997-02-19 | Horne James A | Sleepiness detection for vehicle driver |
US5957958A (en) | 1997-01-15 | 1999-09-28 | Advanced Bionics Corporation | Implantable electrode arrays |
US5860917A (en) | 1997-01-15 | 1999-01-19 | Chiron Corporation | Method and apparatus for predicting therapeutic outcomes |
ES2124186B1 (en) | 1997-01-20 | 1999-08-01 | Carpe Diem Salud S L | SECTION AND TELEMATIC CONTROL SYSTEM OF PHYSIOLOGICAL PARAMETERS OF PATIENTS. |
US5974124A (en) | 1997-01-21 | 1999-10-26 | Med Graph | Method and system aiding medical diagnosis and treatment |
US6122351A (en) | 1997-01-21 | 2000-09-19 | Med Graph, Inc. | Method and system aiding medical diagnosis and treatment |
US5851197A (en) | 1997-02-05 | 1998-12-22 | Minimed Inc. | Injector for a subcutaneous infusion set |
US6607509B2 (en) * | 1997-12-31 | 2003-08-19 | Medtronic Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US6093172A (en) | 1997-02-05 | 2000-07-25 | Minimed Inc. | Injector for a subcutaneous insertion set |
DE69809391T2 (en) | 1997-02-06 | 2003-07-10 | Therasense Inc | SMALL VOLUME SENSOR FOR IN-VITRO DETERMINATION |
US5749907A (en) | 1997-02-18 | 1998-05-12 | Pacesetter, Inc. | System and method for identifying and displaying medical data which violate programmable alarm conditions |
US5785681A (en) | 1997-02-25 | 1998-07-28 | Minimed Inc. | Flow rate controller for a medication infusion pump |
US6164284A (en) | 1997-02-26 | 2000-12-26 | Schulman; Joseph H. | System of implantable devices for monitoring and/or affecting body parameters |
US7114502B2 (en) | 1997-02-26 | 2006-10-03 | Alfred E. Mann Foundation For Scientific Research | Battery-powered patient implantable device |
US6208894B1 (en) | 1997-02-26 | 2001-03-27 | Alfred E. Mann Foundation For Scientific Research And Advanced Bionics | System of implantable devices for monitoring and/or affecting body parameters |
EP1011426A1 (en) | 1997-02-26 | 2000-06-28 | Diasense, Inc. | Individual calibration of blood glucose for supporting noninvasive self-monitoring blood glucose |
US6159147A (en) | 1997-02-28 | 2000-12-12 | Qrs Diagnostics, Llc | Personal computer card for collection of real-time biological data |
US5827179A (en) | 1997-02-28 | 1998-10-27 | Qrs Diagnostic, Llc | Personal computer card for collection for real-time biological data |
US5950632A (en) | 1997-03-03 | 1999-09-14 | Motorola, Inc. | Medical communication apparatus, system, and method |
US6741877B1 (en) | 1997-03-04 | 2004-05-25 | Dexcom, Inc. | Device and method for determining analyte levels |
US20050033132A1 (en) | 1997-03-04 | 2005-02-10 | Shults Mark C. | Analyte measuring device |
US6558321B1 (en) | 1997-03-04 | 2003-05-06 | Dexcom, Inc. | Systems and methods for remote monitoring and modulation of medical devices |
US6862465B2 (en) | 1997-03-04 | 2005-03-01 | Dexcom, Inc. | Device and method for determining analyte levels |
US7657297B2 (en) | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US7192450B2 (en) | 2003-05-21 | 2007-03-20 | Dexcom, Inc. | Porous membranes for use with implantable devices |
US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US5959529A (en) | 1997-03-07 | 1999-09-28 | Kail, Iv; Karl A. | Reprogrammable remote sensor monitoring system |
US6139718A (en) | 1997-03-25 | 2000-10-31 | Cygnus, Inc. | Electrode with improved signal to noise ratio |
US6699187B2 (en) | 1997-03-27 | 2004-03-02 | Medtronic, Inc. | System and method for providing remote expert communications and video capabilities for use during a medical procedure |
US6270455B1 (en) | 1997-03-28 | 2001-08-07 | Health Hero Network, Inc. | Networked system for interactive communications and remote monitoring of drug delivery |
US5961451A (en) | 1997-04-07 | 1999-10-05 | Motorola, Inc. | Noninvasive apparatus having a retaining member to retain a removable biosensor |
US5942979A (en) | 1997-04-07 | 1999-08-24 | Luppino; Richard | On guard vehicle safety warning system |
US5935224A (en) | 1997-04-24 | 1999-08-10 | Microsoft Corporation | Method and apparatus for adaptively coupling an external peripheral device to either a universal serial bus port on a computer or hub or a game port on a computer |
US6248065B1 (en) | 1997-04-30 | 2001-06-19 | Health Hero Network, Inc. | Monitoring system for remotely querying individuals |
US5779665A (en) | 1997-05-08 | 1998-07-14 | Minimed Inc. | Transdermal introducer assembly |
AU7296298A (en) | 1997-05-14 | 1998-12-08 | Sony Electronics Inc. | Antenna arrangement for portable two-way radio apparatus |
AU3128497A (en) | 1997-05-14 | 1998-12-08 | Metrika Laboratories, Inc. | Method and device for producing a predetermined distribution of detectable change in assays |
TW357517B (en) | 1997-05-29 | 1999-05-01 | Koji Akai | Monitoring system |
EP0986757B1 (en) | 1997-06-04 | 2008-02-20 | Sensor Technologies, Inc. | Method and device for detecting or quantifying carbohydrate containing compounds |
US5957890A (en) | 1997-06-09 | 1999-09-28 | Minimed Inc. | Constant flow medication infusion pump |
US7267665B2 (en) | 1999-06-03 | 2007-09-11 | Medtronic Minimed, Inc. | Closed loop system for controlling insulin infusion |
US6558351B1 (en) | 1999-06-03 | 2003-05-06 | Medtronic Minimed, Inc. | Closed loop system for controlling insulin infusion |
US5954643A (en) | 1997-06-09 | 1999-09-21 | Minimid Inc. | Insertion set for a transcutaneous sensor |
ATE489633T1 (en) | 1997-06-10 | 2010-12-15 | Lpath Inc | METHOD FOR EARLY DETECTION OF HEART DISEASES |
US6093167A (en) | 1997-06-16 | 2000-07-25 | Medtronic, Inc. | System for pancreatic stimulation and glucose measurement |
EP0990151A2 (en) | 1997-06-16 | 2000-04-05 | ELAN CORPORATION, Plc | Methods of calibrating and testing a sensor for (in vivo) measurement of an analyte and devices for use in such methods |
US6056435A (en) | 1997-06-24 | 2000-05-02 | Exergen Corporation | Ambient and perfusion normalized temperature detector |
US6651975B2 (en) | 1997-06-27 | 2003-11-25 | Canon Kabushiki Kaisha | Sheet pack and printer |
SE9702658D0 (en) | 1997-07-09 | 1997-07-09 | Thomas Carlsson | Regeneration of biosensors |
US5857967A (en) | 1997-07-09 | 1999-01-12 | Hewlett-Packard Company | Universally accessible healthcare devices with on the fly generation of HTML files |
US6063459A (en) | 1997-07-21 | 2000-05-16 | Velte; Stephen K. | Antenna ornament |
US6066243A (en) | 1997-07-22 | 2000-05-23 | Diametrics Medical, Inc. | Portable immediate response medical analyzer having multiple testing modules |
AU753694B2 (en) | 1997-08-01 | 2002-10-24 | Advanced Bionics Corporation | Implantable device with improved battery recharging and powering configuration |
GB9716254D0 (en) | 1997-08-01 | 1997-10-08 | Hypoguard Uk Ltd | Test device |
WO1999007277A1 (en) | 1997-08-09 | 1999-02-18 | Roche Diagnostics Gmbh | Analytical device for in vivo analysis in the body of a patient |
KR100241052B1 (en) | 1997-08-27 | 2000-02-01 | 박찬구 | Process for preparation of block copolymer |
US6731976B2 (en) | 1997-09-03 | 2004-05-04 | Medtronic, Inc. | Device and method to measure and communicate body parameters |
US6071391A (en) | 1997-09-12 | 2000-06-06 | Nok Corporation | Enzyme electrode structure |
US5917346A (en) | 1997-09-12 | 1999-06-29 | Alfred E. Mann Foundation | Low power current to frequency converter circuit for use in implantable sensors |
US6259937B1 (en) | 1997-09-12 | 2001-07-10 | Alfred E. Mann Foundation | Implantable substrate sensor |
US5999849A (en) | 1997-09-12 | 1999-12-07 | Alfred E. Mann Foundation | Low power rectifier circuit for implantable medical device |
US5999848A (en) | 1997-09-12 | 1999-12-07 | Alfred E. Mann Foundation | Daisy chainable sensors and stimulators for implantation in living tissue |
DE19836401A1 (en) * | 1997-09-19 | 2000-02-17 | Salcomp Oy Salo | Device for charging accumulators |
US6117290A (en) | 1997-09-26 | 2000-09-12 | Pepex Biomedical, Llc | System and method for measuring a bioanalyte such as lactate |
US20020013538A1 (en) * | 1997-09-30 | 2002-01-31 | David Teller | Method and apparatus for health signs monitoring |
AU9599498A (en) | 1997-09-30 | 1999-04-23 | M-Biotech, Inc. | Biosensor |
US6867720B1 (en) | 1997-10-06 | 2005-03-15 | The Regents Of The University Of Michigan | Beamformed ultrasonic imager with delta-sigma feedback control |
US20010032278A1 (en) | 1997-10-07 | 2001-10-18 | Brown Stephen J. | Remote generation and distribution of command programs for programmable devices |
US6097831A (en) | 1997-10-14 | 2000-08-01 | Chiron Corporation | Non-contract method for assay reagent volume dispense verification |
EP0918423B1 (en) * | 1997-10-15 | 2004-03-10 | Nokia Corporation | Mobile phone for Internet applications |
US6119028A (en) | 1997-10-20 | 2000-09-12 | Alfred E. Mann Foundation | Implantable enzyme-based monitoring systems having improved longevity due to improved exterior surfaces |
US6088608A (en) | 1997-10-20 | 2000-07-11 | Alfred E. Mann Foundation | Electrochemical sensor and integrity tests therefor |
US6081736A (en) | 1997-10-20 | 2000-06-27 | Alfred E. Mann Foundation | Implantable enzyme-based monitoring systems adapted for long term use |
FI107080B (en) | 1997-10-27 | 2001-05-31 | Nokia Mobile Phones Ltd | measuring device |
US6144922A (en) | 1997-10-31 | 2000-11-07 | Mercury Diagnostics, Incorporated | Analyte concentration information collection and communication system |
EP1025530A2 (en) | 1997-10-31 | 2000-08-09 | Amira Medical | Analyte concentration information collection and communication s ystem |
US5931791A (en) | 1997-11-05 | 1999-08-03 | Instromedix, Inc. | Medical patient vital signs-monitoring apparatus |
JPH11141577A (en) | 1997-11-05 | 1999-05-25 | Nsk Warner Kk | One-way clutch |
US6044285A (en) | 1997-11-12 | 2000-03-28 | Lightouch Medical, Inc. | Method for non-invasive measurement of an analyte |
US5971941A (en) | 1997-12-04 | 1999-10-26 | Hewlett-Packard Company | Integrated system and method for sampling blood and analysis |
CA2547299C (en) | 1997-12-04 | 2009-03-03 | Roche Diagnostics Corporation | Instrument and method |
US6071294A (en) | 1997-12-04 | 2000-06-06 | Agilent Technologies, Inc. | Lancet cartridge for sampling blood |
US6579690B1 (en) | 1997-12-05 | 2003-06-17 | Therasense, Inc. | Blood analyte monitoring through subcutaneous measurement |
US6033866A (en) | 1997-12-08 | 2000-03-07 | Biomedix, Inc. | Highly sensitive amperometric bi-mediator-based glucose biosensor |
EP1038176B1 (en) | 1997-12-19 | 2003-11-12 | Amira Medical | Embossed test strip system |
US6198957B1 (en) | 1997-12-19 | 2001-03-06 | Varian, Inc. | Radiotherapy machine including magnetic resonance imaging system |
ES2326145T3 (en) | 1997-12-22 | 2009-10-01 | Roche Diagnostics Operations, Inc. | Measuring device. |
US6073031A (en) | 1997-12-24 | 2000-06-06 | Nortel Networks Corporation | Desktop docking station for use with a wireless telephone handset |
US6055316A (en) | 1997-12-26 | 2000-04-25 | Sun Microsystems, Inc. | System and method for deriving an appropriate initialization vector for secure communications |
EP2201969B1 (en) | 1997-12-31 | 2011-03-30 | Medtronic MiniMed, Inc. | Insertion device for an insertion set |
CA2484271C (en) | 1997-12-31 | 2007-04-24 | Medtronic Minimed, Inc. | Insertion device for an insertion set and method of using the same |
US6110152A (en) | 1998-01-13 | 2000-08-29 | Minimed Inc. | Medication cartridge for an electronic pen-type injector, infusion pump, electronic delivery device, or the like, and method of making the same |
US5954700A (en) | 1998-01-13 | 1999-09-21 | Minimed Inc. | Medication cartridge for an electronic pen-type injector, or the like, and method of making the same |
KR100324159B1 (en) | 1998-01-21 | 2002-02-16 | 니시무로 타이죠 | Video data recording medium, video data recording apparatus and video data playback apparatus |
US6097480A (en) | 1998-01-27 | 2000-08-01 | Kaplan; Milton | Vehicle interlock system |
US7222054B2 (en) | 1998-03-03 | 2007-05-22 | Card Guard Scientific Survival Ltd. | Personal ambulatory wireless health monitor |
US6056718A (en) | 1998-03-04 | 2000-05-02 | Minimed Inc. | Medication infusion set |
US6103033A (en) | 1998-03-04 | 2000-08-15 | Therasense, Inc. | Process for producing an electrochemical biosensor |
US6134461A (en) | 1998-03-04 | 2000-10-17 | E. Heller & Company | Electrochemical analyte |
WO1999044507A1 (en) | 1998-03-06 | 1999-09-10 | Spectrx, Inc. | Integrated tissue poration, fluid harvesting and analysis device, and method therefor |
US6530915B1 (en) | 1998-03-06 | 2003-03-11 | Spectrx, Inc. | Photothermal structure for biomedical applications, and method therefor |
US6587705B1 (en) | 1998-03-13 | 2003-07-01 | Lynn Kim | Biosensor, iontophoretic sampling system, and methods of use thereof |
US6024699A (en) | 1998-03-13 | 2000-02-15 | Healthware Corporation | Systems, methods and computer program products for monitoring, diagnosing and treating medical conditions of remotely located patients |
GB9805896D0 (en) | 1998-03-20 | 1998-05-13 | Eglise David | Remote analysis system |
US6218809B1 (en) | 1998-03-20 | 2001-04-17 | Dallas Semiconductor Corporation | Method for monitoring operating parameters of a rechargeable power supply |
US5939609A (en) | 1998-03-23 | 1999-08-17 | Conception Technology Incorporated | Multi-use sensor having a controllable number of measurement cycles |
US6579231B1 (en) | 1998-03-27 | 2003-06-17 | Mci Communications Corporation | Personal medical monitoring unit and system |
JP3104672B2 (en) | 1998-03-31 | 2000-10-30 | 日本電気株式会社 | Current detection type sensor element and method of manufacturing the same |
US6091975A (en) | 1998-04-01 | 2000-07-18 | Alza Corporation | Minimally invasive detecting device |
US6728560B2 (en) | 1998-04-06 | 2004-04-27 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
US6505059B1 (en) | 1998-04-06 | 2003-01-07 | The General Hospital Corporation | Non-invasive tissue glucose level monitoring |
JPH11296598A (en) | 1998-04-07 | 1999-10-29 | Seizaburo Arita | System and method for predicting blood-sugar level and record medium where same method is recorded |
CA2325886C (en) | 1998-04-09 | 2009-07-21 | California Institute Of Technology | Electronic techniques for analyte detection |
US7647237B2 (en) | 1998-04-29 | 2010-01-12 | Minimed, Inc. | Communication station and software for interfacing with an infusion pump, analyte monitor, analyte meter, or the like |
US6091987A (en) | 1998-04-29 | 2000-07-18 | Medtronic, Inc. | Power consumption reduction in medical devices by employing different supply voltages |
US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
WO1999058190A1 (en) | 1998-05-13 | 1999-11-18 | Cygnus, Inc. | Collection assemblies for transdermal sampling system |
WO1999058050A1 (en) | 1998-05-13 | 1999-11-18 | Cygnus, Inc. | Signal processing for measurement of physiological analytes |
EP1077634B1 (en) * | 1998-05-13 | 2003-07-30 | Cygnus, Inc. | Monitoring of physiological analytes |
ATE246356T1 (en) | 1998-05-13 | 2003-08-15 | Cygnus Therapeutic Systems | DEVICE FOR PREDICTING PHYSIOLOGICAL MEASUREMENTS |
US6307867B1 (en) | 1998-05-14 | 2001-10-23 | Telefonaktiebolaget Lm Ericsson (Publ) | Data transmission over a communications link with variable transmission rates |
US6121611A (en) | 1998-05-20 | 2000-09-19 | Molecular Imaging Corporation | Force sensing probe for scanning probe microscopy |
WO1999060391A1 (en) | 1998-05-20 | 1999-11-25 | Arkray, Inc. | Method and apparatus for electrochemical measurement using statistical technique |
US6302855B1 (en) * | 1998-05-20 | 2001-10-16 | Novo Nordisk A/S | Medical apparatus for use by a patient for medical self treatment of diabetes |
US6246330B1 (en) | 1998-05-29 | 2001-06-12 | Wyn Y. Nielsen | Elimination-absorber monitoring system |
US6301499B1 (en) | 1998-06-08 | 2001-10-09 | Cardiac Pacemakers, Inc. | Heart rate variability as an indicator of exercise capacity |
US6026320A (en) | 1998-06-08 | 2000-02-15 | Cardiac Pacemakers, Inc. | Heart rate variability as an indicator of exercise capacity |
US6294281B1 (en) | 1998-06-17 | 2001-09-25 | Therasense, Inc. | Biological fuel cell and method |
US6736797B1 (en) | 1998-06-19 | 2004-05-18 | Unomedical A/S | Subcutaneous infusion set |
US6280587B1 (en) | 1998-07-02 | 2001-08-28 | Nec Corporation | Enzyme electrode and a biosensor and a measuring apparatus therewith |
JP2000031951A (en) | 1998-07-15 | 2000-01-28 | Fujitsu Ltd | Burst synchronization circuit |
US7384396B2 (en) | 1998-07-21 | 2008-06-10 | Spectrx Inc. | System and method for continuous analyte monitoring |
US6493069B1 (en) | 1998-07-24 | 2002-12-10 | Terumo Kabushiki Kaisha | Method and instrument for measuring blood sugar level |
US6267724B1 (en) | 1998-07-30 | 2001-07-31 | Microfab Technologies, Inc. | Implantable diagnostic sensor |
US6558320B1 (en) | 2000-01-20 | 2003-05-06 | Medtronic Minimed, Inc. | Handheld personal data assistant (PDA) with a medical device and method of using the same |
US6248067B1 (en) | 1999-02-05 | 2001-06-19 | Minimed Inc. | Analyte sensor and holter-type monitor system and method of using the same |
US6554798B1 (en) | 1998-08-18 | 2003-04-29 | Medtronic Minimed, Inc. | External infusion device with remote programming, bolus estimator and/or vibration alarm capabilities |
US6535753B1 (en) | 1998-08-20 | 2003-03-18 | Microsense International, Llc | Micro-invasive method for painless detection of analytes in extra-cellular space |
US6281006B1 (en) | 1998-08-24 | 2001-08-28 | Therasense, Inc. | Electrochemical affinity assay |
US6251260B1 (en) | 1998-08-24 | 2001-06-26 | Therasense, Inc. | Potentiometric sensors for analytic determination |
ES2306525T3 (en) | 1998-08-26 | 2008-11-01 | Sensors For Medicine And Science, Inc. | OPTICAL-BASED DETECTION DEVICES. |
US6304766B1 (en) | 1998-08-26 | 2001-10-16 | Sensors For Medicine And Science | Optical-based sensing devices, especially for in-situ sensing in humans |
US6266645B1 (en) | 1998-09-01 | 2001-07-24 | Imetrikus, Inc. | Risk adjustment tools for analyzing patient electronic discharge records |
US6464848B1 (en) | 1998-09-03 | 2002-10-15 | Nec Corporation | Reference electrode, a biosensor and a measuring apparatus therewith |
CA2342801A1 (en) | 1998-09-04 | 2000-03-16 | Powderject Research Limited | Monitoring methods using particle delivery methods |
US6602678B2 (en) | 1998-09-04 | 2003-08-05 | Powderject Research Limited | Non- or minimally invasive monitoring methods |
US6480753B1 (en) * | 1998-09-04 | 2002-11-12 | Ncr Corporation | Communications, particularly in the domestic environment |
DE19840965A1 (en) | 1998-09-08 | 2000-03-09 | Disetronic Licensing Ag | Device for self-administration of a product fluid |
US6918874B1 (en) | 1998-09-10 | 2005-07-19 | Spectrx, Inc. | Attribute compensation for analyte detection and/or continuous monitoring |
WO2000013580A1 (en) | 1998-09-11 | 2000-03-16 | Amira Medical | Device for determination of an analyte in a body fluid intergrated with an insulin pump |
KR20000019716A (en) | 1998-09-15 | 2000-04-15 | 박호군 | Composition comprising bioflavonoid compounds for descending blood sugar |
ATE254877T1 (en) | 1998-09-17 | 2003-12-15 | Cygnus Therapeutic Systems | DEVICE FOR PRESSING A GEL/SENSOR UNIT |
US6740518B1 (en) | 1998-09-17 | 2004-05-25 | Clinical Micro Sensors, Inc. | Signal detection techniques for the detection of analytes |
US6853854B1 (en) | 1998-09-18 | 2005-02-08 | Q Step Technologies, Llc | Noninvasive measurement system |
US6254586B1 (en) | 1998-09-25 | 2001-07-03 | Minimed Inc. | Method and kit for supplying a fluid to a subcutaneous placement site |
US5951521A (en) | 1998-09-25 | 1999-09-14 | Minimed Inc. | Subcutaneous implantable sensor set having the capability to remove deliver fluids to an insertion site |
WO2000018294A1 (en) | 1998-09-30 | 2000-04-06 | Sicel Medical Group | Methods, systems, and associated implantable devices for dynamic monitoring of tumors |
US6442672B1 (en) | 1998-09-30 | 2002-08-27 | Conexant Systems, Inc. | Method for dynamic allocation and efficient sharing of functional unit datapaths |
US6180416B1 (en) | 1998-09-30 | 2001-01-30 | Cygnus, Inc. | Method and device for predicting physiological values |
DE69908602T2 (en) | 1998-09-30 | 2004-06-03 | Cygnus, Inc., Redwood City | METHOD AND DEVICE FOR PREDICTING PHYSIOLOGICAL MEASUREMENTS |
US6402689B1 (en) | 1998-09-30 | 2002-06-11 | Sicel Technologies, Inc. | Methods, systems, and associated implantable devices for dynamic monitoring of physiological and biological properties of tumors |
US6201980B1 (en) | 1998-10-05 | 2001-03-13 | The Regents Of The University Of California | Implantable medical sensor system |
US6338790B1 (en) | 1998-10-08 | 2002-01-15 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
WO2000019887A1 (en) * | 1998-10-08 | 2000-04-13 | Minimed Inc. | Telemetered characteristic monitor system |
US20060202859A1 (en) | 1998-10-08 | 2006-09-14 | Mastrototaro John J | Telemetered characteristic monitor system and method of using the same |
US6591125B1 (en) | 2000-06-27 | 2003-07-08 | Therasense, Inc. | Small volume in vitro analyte sensor with diffusible or non-leachable redox mediator |
US6391643B1 (en) | 1998-10-28 | 2002-05-21 | Cygnus, Inc. | Kit and method for quality control testing of an iontophoretic sampling system |
US6496729B2 (en) | 1998-10-28 | 2002-12-17 | Medtronic, Inc. | Power consumption reduction in medical devices employing multiple supply voltages and clock frequency control |
US6248093B1 (en) | 1998-10-29 | 2001-06-19 | Minimed Inc. | Compact pump drive system |
EP1126779A4 (en) | 1998-11-03 | 2003-05-07 | Shell Allan Michael | Hand held physiological signal acquisition device |
US6497729B1 (en) | 1998-11-20 | 2002-12-24 | The University Of Connecticut | Implant coating for control of tissue/implant interactions |
US6540672B1 (en) * | 1998-12-09 | 2003-04-01 | Novo Nordisk A/S | Medical system and a method of controlling the system for use by a patient for medical self treatment |
HUP0104660A2 (en) | 1998-11-30 | 2002-03-28 | Novo Nordisk A/S | A method and a system for assisting a user in a medical self treatment, said self treatment comprising a plurality of actions |
US6161095A (en) | 1998-12-16 | 2000-12-12 | Health Hero Network, Inc. | Treatment regimen compliance and efficacy with feedback |
JP2002531194A (en) | 1998-12-02 | 2002-09-24 | ユーティー−バトル,エルエルシー | In vivo biosensor device and method of use |
US6329929B1 (en) | 1998-12-21 | 2001-12-11 | Medtronic Inc. | Telemetry system with phase-locking noise suppressing receiver |
WO2000045897A1 (en) | 1999-02-03 | 2000-08-10 | Synergy Innovations, Inc. | In-bed exercise machine and method of use |
EP1135052A1 (en) | 1999-02-12 | 2001-09-26 | Cygnus, Inc. | Devices and methods for frequent measurement of an analyte present in a biological system |
JP2002537031A (en) | 1999-02-18 | 2002-11-05 | バイオバルブ テクノロジーズ インコーポレイテッド | Electroactive pores |
US6283943B1 (en) | 1999-02-19 | 2001-09-04 | Minimed Inc. | Negative pressure pump |
US6280416B1 (en) | 1999-02-19 | 2001-08-28 | Minimed Inc. | Constant flow medication infusion pump |
US6360888B1 (en) | 1999-02-25 | 2002-03-26 | Minimed Inc. | Glucose sensor package system |
US6424847B1 (en) | 1999-02-25 | 2002-07-23 | Medtronic Minimed, Inc. | Glucose monitor calibration methods |
JP4801839B2 (en) | 1999-02-25 | 2011-10-26 | メドトロニック ミニメド インコーポレイテッド | Test plug and cable for glucose monitor |
US7089780B2 (en) | 1999-03-03 | 2006-08-15 | Smiths Detection Inc. | Apparatus, systems and methods for detecting and transmitting sensory data over a computer network |
US8103325B2 (en) * | 1999-03-08 | 2012-01-24 | Tyco Healthcare Group Lp | Method and circuit for storing and providing historical physiological data |
TW537880B (en) | 1999-03-11 | 2003-06-21 | Remote Medical Corp | Method for improving patient compliance with a medical program |
US20010049096A1 (en) | 1999-03-23 | 2001-12-06 | Stephen J. Brown | Sample identification with analyte determination |
US6704587B1 (en) | 1999-04-01 | 2004-03-09 | Spectrx, Inc. | Dual function assay device |
AU4063100A (en) | 1999-04-01 | 2000-10-23 | University Of Connecticut, The | Optical glucose sensor apparatus and method |
GB9907815D0 (en) | 1999-04-06 | 1999-06-02 | Univ Cambridge Tech | Implantable sensor |
US6285897B1 (en) | 1999-04-07 | 2001-09-04 | Endonetics, Inc. | Remote physiological monitoring system |
US6336900B1 (en) | 1999-04-12 | 2002-01-08 | Agilent Technologies, Inc. | Home hub for reporting patient health parameters |
US6385473B1 (en) | 1999-04-15 | 2002-05-07 | Nexan Limited | Physiological sensor device |
US6494829B1 (en) | 1999-04-15 | 2002-12-17 | Nexan Limited | Physiological sensor array |
US6416471B1 (en) | 1999-04-15 | 2002-07-09 | Nexan Limited | Portable remote patient telemonitoring system |
US6200265B1 (en) | 1999-04-16 | 2001-03-13 | Medtronic, Inc. | Peripheral memory patch and access method for use with an implantable medical device |
CA2369336A1 (en) | 1999-04-22 | 2000-11-02 | Cygnus, Inc. | Hydrogel in an iontophoretic device to measure glucose |
US6192891B1 (en) | 1999-04-26 | 2001-02-27 | Becton Dickinson And Company | Integrated system including medication delivery pen, blood monitoring device, and lancer |
US6449255B1 (en) | 1999-04-26 | 2002-09-10 | Cisco Technology, Inc. | Method and apparatus for managing packets using a real-time feedback signal |
US6669663B1 (en) | 1999-04-30 | 2003-12-30 | Medtronic, Inc. | Closed loop medicament pump |
US6858403B2 (en) | 1999-05-11 | 2005-02-22 | M-Biotech, Inc. | Polymer matrix containing catalase co-immobilized with analytic enzyme that generates hydrogen peroxide |
US6835553B2 (en) | 1999-05-11 | 2004-12-28 | M-Biotech, Inc. | Photometric glucose measurement system using glucose-sensitive hydrogel |
US6475750B1 (en) | 1999-05-11 | 2002-11-05 | M-Biotech, Inc. | Glucose biosensor |
US6546268B1 (en) | 1999-06-02 | 2003-04-08 | Ball Semiconductor, Inc. | Glucose sensor |
US7806886B2 (en) | 1999-06-03 | 2010-10-05 | Medtronic Minimed, Inc. | Apparatus and method for controlling insulin infusion with state variable feedback |
US6312378B1 (en) * | 1999-06-03 | 2001-11-06 | Cardiac Intelligence Corporation | System and method for automated collection and analysis of patient information retrieved from an implantable medical device for remote patient care |
US6193873B1 (en) | 1999-06-15 | 2001-02-27 | Lifescan, Inc. | Sample detection to initiate timing of an electrochemical assay |
US6259587B1 (en) | 1999-06-17 | 2001-07-10 | Minimed Inc. | Direct current motor safety circuits for fluid delivery systems |
WO2000078210A1 (en) | 1999-06-17 | 2000-12-28 | Minimed Inc. | Characteristic monitor system for use with analyte sensor |
JP4801301B2 (en) | 1999-06-18 | 2011-10-26 | アボット ダイアベティス ケア インコーポレイテッド | In vivo analyte sensor with limited mass transfer |
US6423035B1 (en) | 1999-06-18 | 2002-07-23 | Animas Corporation | Infusion pump with a sealed drive mechanism and improved method of occlusion detection |
US6907127B1 (en) | 1999-06-18 | 2005-06-14 | Digital Video Express, L.P. | Hierarchical key management encoding and decoding |
US7522878B2 (en) * | 1999-06-21 | 2009-04-21 | Access Business Group International Llc | Adaptive inductive power supply with communication |
US6368274B1 (en) | 1999-07-01 | 2002-04-09 | Medtronic Minimed, Inc. | Reusable analyte sensor site and method of using the same |
US6804558B2 (en) | 1999-07-07 | 2004-10-12 | Medtronic, Inc. | System and method of communicating between an implantable medical device and a remote computer system or health care provider |
US6413393B1 (en) | 1999-07-07 | 2002-07-02 | Minimed, Inc. | Sensor including UV-absorbing polymer and method of manufacture |
US6252032B1 (en) | 1999-07-07 | 2001-06-26 | Minimed Inc. | UV absorbing polymer |
DE19935165A1 (en) | 1999-07-28 | 2001-02-01 | Roche Diagnostics Gmbh | Method and arrangement for determining the concentration of glucose in a body fluid |
US6468222B1 (en) | 1999-08-02 | 2002-10-22 | Healthetech, Inc. | Metabolic calorimeter employing respiratory gas analysis |
US6899684B2 (en) | 1999-08-02 | 2005-05-31 | Healthetech, Inc. | Method of respiratory gas analysis using a metabolic calorimeter |
DE60019174T2 (en) | 1999-08-06 | 2005-08-11 | Matsushita Electric Industrial Co., Ltd., Kadoma | Data transmission method, apparatus and data receiving apparatus |
US6442637B1 (en) | 1999-08-12 | 2002-08-27 | Handspring, Inc. | Expandable mobile computer system |
US6471689B1 (en) | 1999-08-16 | 2002-10-29 | Thomas Jefferson University | Implantable drug delivery catheter system with capillary interface |
US7113821B1 (en) | 1999-08-25 | 2006-09-26 | Johnson & Johnson Consumer Companies, Inc. | Tissue electroperforation for enhanced drug delivery |
US7133717B2 (en) | 1999-08-25 | 2006-11-07 | Johnson & Johnson Consumer Companies, Inc. | Tissue electroperforation for enhanced drug delivery and diagnostic sampling |
US6608562B1 (en) | 1999-08-31 | 2003-08-19 | Denso Corporation | Vital signal detecting apparatus |
US6239925B1 (en) | 1999-09-03 | 2001-05-29 | Key Plastics, Inc. | Instrument cluster lens assembly and method of making |
US6366793B1 (en) | 1999-09-10 | 2002-04-02 | Beckman Coulter, Inc. | Minimally invasive methods for measuring analtes in vivo |
US20030175993A1 (en) | 1999-09-10 | 2003-09-18 | Anthony Toranto | Ketone assay |
US6673625B2 (en) | 1999-09-15 | 2004-01-06 | The Regents Of The University Of California | Saccharide sensing molecules having enhanced fluorescent properties |
US6682938B1 (en) | 1999-09-15 | 2004-01-27 | The Regents Of The University Of California | Glucose sensing molecules having selected fluorescent properties |
AT408182B (en) | 1999-09-17 | 2001-09-25 | Schaupp Lukas Dipl Ing Dr Tech | DEVICE FOR VIVO MEASURING SIZES IN LIVING ORGANISMS |
WO2001028416A1 (en) | 1999-09-24 | 2001-04-26 | Healthetech, Inc. | Physiological monitor and associated computation, display and communication unit |
AU7718500A (en) | 1999-09-28 | 2001-04-30 | Imetrikus, Inc. | Internet brokering service based upon individual health profiles |
US6294997B1 (en) | 1999-10-04 | 2001-09-25 | Intermec Ip Corp. | RFID tag having timing and environment modules |
US20020107433A1 (en) | 1999-10-08 | 2002-08-08 | Mault James R. | System and method of personal fitness training using interactive television |
US20020062069A1 (en) | 1999-10-08 | 2002-05-23 | Mault James R. | System and method of integrated calorie management using interactive television |
US6478736B1 (en) | 1999-10-08 | 2002-11-12 | Healthetech, Inc. | Integrated calorie management system |
CA2386811A1 (en) | 1999-10-08 | 2001-04-19 | Healthetech, Inc. | Monitoring caloric expenditure rate and caloric diet |
US6612306B1 (en) | 1999-10-13 | 2003-09-02 | Healthetech, Inc. | Respiratory nitric oxide meter |
US7039810B1 (en) | 1999-11-02 | 2006-05-02 | Medtronic, Inc. | Method and apparatus to secure data transfer from medical device systems |
US6616819B1 (en) | 1999-11-04 | 2003-09-09 | Therasense, Inc. | Small volume in vitro analyte sensor and methods |
US6253804B1 (en) | 1999-11-05 | 2001-07-03 | Minimed Inc. | Needle safe transfer guard |
AU1607801A (en) | 1999-11-15 | 2001-05-30 | Therasense, Inc. | Transition metal complexes with bidentate ligand having an imidazole ring |
US6291200B1 (en) | 1999-11-17 | 2001-09-18 | Agentase, Llc | Enzyme-containing polymeric sensors |
US6658396B1 (en) | 1999-11-29 | 2003-12-02 | Tang Sharon S | Neural network drug dosage estimation |
US6359594B1 (en) * | 1999-12-01 | 2002-03-19 | Logitech Europe S.A. | Loop antenna parasitics reduction technique |
US6418346B1 (en) | 1999-12-14 | 2002-07-09 | Medtronic, Inc. | Apparatus and method for remote therapy and diagnosis in medical devices via interface systems |
US6497655B1 (en) | 1999-12-17 | 2002-12-24 | Medtronic, Inc. | Virtual remote monitor, alert, diagnostics and programming for implantable medical device systems |
US7060031B2 (en) | 1999-12-17 | 2006-06-13 | Medtronic, Inc. | Method and apparatus for remotely programming implantable medical devices |
US6602191B2 (en) * | 1999-12-17 | 2003-08-05 | Q-Tec Systems Llp | Method and apparatus for health and disease management combining patient data monitoring with wireless internet connectivity |
DE19962342A1 (en) | 1999-12-23 | 2001-07-12 | Henkel Ecolab Gmbh & Co Ohg | Peracids with good adhesion to surfaces |
DE19962343A1 (en) | 1999-12-23 | 2001-07-05 | Henkel Ecolab Gmbh & Co Ohg | Disinfectant washing of delicate textiles with peracids |
US20020091796A1 (en) | 2000-01-03 | 2002-07-11 | John Higginson | Method and apparatus for transmitting data over a network using a docking device |
US6295463B1 (en) | 2000-01-04 | 2001-09-25 | Sensormedics Corporation | Skin protection mount for transcutaneous sensor application |
US7286894B1 (en) | 2000-01-07 | 2007-10-23 | Pasco Scientific | Hand-held computer device and method for interactive data acquisition, analysis, annotation, and calibration |
US6513532B2 (en) | 2000-01-19 | 2003-02-04 | Healthetech, Inc. | Diet and activity-monitoring device |
US6383767B1 (en) | 2000-01-21 | 2002-05-07 | Motorola, Inc. | Luminescent in vivo glucose measurement |
ATE552869T1 (en) | 2000-01-21 | 2012-04-15 | Medtronic Minimed Inc | MICROPROCESSOR-CONTROLLED, AMBULATORY MEDICAL DEVICE WITH HAND-HOLD COMMUNICATION DEVICE |
US7369635B2 (en) | 2000-01-21 | 2008-05-06 | Medtronic Minimed, Inc. | Rapid discrimination preambles and methods for using the same |
WO2001052935A1 (en) | 2000-01-21 | 2001-07-26 | Medical Research Group, Inc. | Ambulatory medical apparatus and method having telemetry modifiable control software |
US6974437B2 (en) | 2000-01-21 | 2005-12-13 | Medtronic Minimed, Inc. | Microprocessor controlled ambulatory medical apparatus with hand held communication device |
US6734162B2 (en) | 2000-01-24 | 2004-05-11 | Minimed Inc. | Mixed buffer system for stabilizing polypeptide formulations |
US6748445B1 (en) | 2000-02-01 | 2004-06-08 | Microsoft Corporation | System and method for exchanging data |
US6485923B1 (en) | 2000-02-02 | 2002-11-26 | Lifescan, Inc. | Reagent test strip for analyte determination having hemolyzing agent |
US6716577B1 (en) | 2000-02-02 | 2004-04-06 | Lifescan, Inc. | Electrochemical test strip for use in analyte determination |
US6629934B2 (en) | 2000-02-02 | 2003-10-07 | Healthetech, Inc. | Indirect calorimeter for medical applications |
US20010037060A1 (en) | 2000-02-08 | 2001-11-01 | Thompson Richard P. | Web site for glucose monitoring |
US7003336B2 (en) | 2000-02-10 | 2006-02-21 | Medtronic Minimed, Inc. | Analyte sensor method of making the same |
US6484045B1 (en) | 2000-02-10 | 2002-11-19 | Medtronic Minimed, Inc. | Analyte sensor and method of making the same |
US20030060765A1 (en) | 2000-02-16 | 2003-03-27 | Arthur Campbell | Infusion device menu structure and method of using the same |
WO2001060448A1 (en) | 2000-02-18 | 2001-08-23 | University Of Utah Research Foundation | Methods for extracting substances using alternating current |
US6895263B2 (en) | 2000-02-23 | 2005-05-17 | Medtronic Minimed, Inc. | Real time self-adjusting calibration algorithm |
US7890295B2 (en) | 2000-02-23 | 2011-02-15 | Medtronic Minimed, Inc. | Real time self-adjusting calibration algorithm |
US7027931B1 (en) | 2000-02-24 | 2006-04-11 | Bionostics, Inc. | System for statistical analysis of quality control data |
US6893396B2 (en) * | 2000-03-01 | 2005-05-17 | I-Medik, Inc. | Wireless internet bio-telemetry monitoring system and interface |
US6706159B2 (en) | 2000-03-02 | 2004-03-16 | Diabetes Diagnostics | Combined lancet and electrochemical analyte-testing apparatus |
FR2806156B1 (en) | 2000-03-07 | 2002-05-31 | Ciat Sa | PLATE HEAT EXCHANGER |
US20010039504A1 (en) | 2000-03-15 | 2001-11-08 | Linberg Kurt R. | Individualized, integrated and informative internet portal for holistic management of patients with implantable devices |
US6405066B1 (en) | 2000-03-17 | 2002-06-11 | The Regents Of The University Of California | Implantable analyte sensor |
EP1136033B1 (en) | 2000-03-21 | 2004-11-10 | Radi Medical Systems Ab | Passive biotelemetry |
DZ3338A1 (en) | 2000-03-29 | 2001-10-04 | Univ Virginia | METHOD, SYSTEM AND COMPUTER PROGRAM FOR EVALUATING GLYCEMIC REGULATION OF DIABETES FROM AUTOMATICALLY CONTROLLED DATA |
US6610012B2 (en) | 2000-04-10 | 2003-08-26 | Healthetech, Inc. | System and method for remote pregnancy monitoring |
US6441747B1 (en) | 2000-04-18 | 2002-08-27 | Motorola, Inc. | Wireless system protocol for telemetry monitoring |
US6561975B1 (en) | 2000-04-19 | 2003-05-13 | Medtronic, Inc. | Method and apparatus for communicating with medical device systems |
US6616613B1 (en) | 2000-04-27 | 2003-09-09 | Vitalsines International, Inc. | Physiological signal monitoring system |
US6440068B1 (en) | 2000-04-28 | 2002-08-27 | International Business Machines Corporation | Measuring user health as measured by multiple diverse health measurement devices utilizing a personal storage device |
IT1314759B1 (en) | 2000-05-08 | 2003-01-03 | Menarini Farma Ind | INSTRUMENTATION FOR MEASUREMENT AND CONTROL OF THE CONTENT OF GLUCOSIOLACTATE OR OTHER METABOLITES IN BIOLOGICAL FLUIDS |
AU2001263022A1 (en) | 2000-05-12 | 2001-11-26 | Therasense, Inc. | Electrodes with multilayer membranes and methods of using and making the electrodes |
US6442413B1 (en) | 2000-05-15 | 2002-08-27 | James H. Silver | Implantable sensor |
US7181261B2 (en) | 2000-05-15 | 2007-02-20 | Silver James H | Implantable, retrievable, thrombus minimizing sensors |
US6340421B1 (en) | 2000-05-16 | 2002-01-22 | Minimed Inc. | Microelectrogravimetric method for plating a biosensor |
US6885883B2 (en) | 2000-05-16 | 2005-04-26 | Cygnus, Inc. | Methods for improving performance and reliability of biosensors |
US6482158B2 (en) | 2000-05-19 | 2002-11-19 | Healthetech, Inc. | System and method of ultrasonic mammography |
EP1283689A4 (en) | 2000-05-25 | 2005-03-09 | Healthetech Inc | Weight control method using physical activity based parameters |
EP1284642A4 (en) | 2000-05-25 | 2005-03-09 | Healthetech Inc | Physiological monitoring using wrist-mounted device |
AU2001260710A1 (en) | 2000-06-02 | 2001-12-11 | Arkray, Inc. | Measurement device, and measured data transmitting method |
WO2001093743A2 (en) | 2000-06-07 | 2001-12-13 | Healthetech, Inc. | Breath ketone analyzer |
US6735479B2 (en) * | 2000-06-14 | 2004-05-11 | Medtronic, Inc. | Lifestyle management system |
WO2001096024A2 (en) | 2000-06-14 | 2001-12-20 | Board Of Regents, The University Of Texas System | Apparatus and method for fluid injection |
US7261690B2 (en) | 2000-06-16 | 2007-08-28 | Bodymedia, Inc. | Apparatus for monitoring health, wellness and fitness |
US20020016719A1 (en) | 2000-06-19 | 2002-02-07 | Nemeth Louis G. | Methods and systems for providing medical data to a third party in accordance with configurable distribution parameters |
US6699188B2 (en) | 2000-06-22 | 2004-03-02 | Guidance Interactive Technologies | Interactive reward devices and methods |
US6494830B1 (en) | 2000-06-22 | 2002-12-17 | Guidance Interactive Technologies, Inc. | Handheld controller for monitoring/using medical parameters |
IL153516A (en) * | 2000-06-23 | 2007-07-24 | Bodymedia Inc | System for monitoring health, wellness and fitness |
US6540675B2 (en) | 2000-06-27 | 2003-04-01 | Rosedale Medical, Inc. | Analyte monitor |
US6400974B1 (en) | 2000-06-29 | 2002-06-04 | Sensors For Medicine And Science, Inc. | Implanted sensor processing system and method for processing implanted sensor output |
US6580364B1 (en) | 2000-07-06 | 2003-06-17 | Trw Inc. | Apparatus and method for tracking an abnormal tire condition |
DE10038835B4 (en) | 2000-08-04 | 2005-07-07 | Roche Diagnostics Gmbh | Microdialysis system |
WO2002012251A1 (en) | 2000-08-04 | 2002-02-14 | Sensors For Medicine And Science, Inc. | Detection of analytes in aqueous environments |
JP2002055076A (en) | 2000-09-08 | 2002-02-20 | Nec Corp | Electrochemical sensor |
WO2002015777A1 (en) | 2000-08-18 | 2002-02-28 | Cygnus, Inc. | Methods and devices for prediction of hypoglycemic events |
WO2002017210A2 (en) | 2000-08-18 | 2002-02-28 | Cygnus, Inc. | Formulation and manipulation of databases of analyte and associated values |
US6553244B2 (en) | 2000-08-18 | 2003-04-22 | Cygnus, Inc. | Analyte monitoring device alarm augmentation system |
US6675030B2 (en) | 2000-08-21 | 2004-01-06 | Euro-Celtique, S.A. | Near infrared blood glucose monitoring system |
US20020026111A1 (en) | 2000-08-28 | 2002-02-28 | Neil Ackerman | Methods of monitoring glucose levels in a subject and uses thereof |
US20020026937A1 (en) | 2000-08-28 | 2002-03-07 | Mault James R. | Respiratory gas sensors in folw path |
DE10042367A1 (en) | 2000-08-29 | 2002-05-02 | Bosch Gmbh Robert | Method and device for diagnosing a driver's ability to drive in a motor vehicle |
US6741876B1 (en) | 2000-08-31 | 2004-05-25 | Cme Telemetrix Inc. | Method for determination of analytes using NIR, adjacent visible spectrum and discrete NIR wavelenths |
US20020047867A1 (en) | 2000-09-07 | 2002-04-25 | Mault James R | Image based diet logging |
AU2001291189A1 (en) | 2000-09-22 | 2002-04-02 | Knobbe, Lim And Buckingham | Method and apparatus for real-time estimation and control of pysiological parameters |
US20020124017A1 (en) | 2000-09-22 | 2002-09-05 | Mault James R. | Personal digital assistant with food scale accessory |
US20020103425A1 (en) | 2000-09-27 | 2002-08-01 | Mault James R. | self-contained monitoring device particularly useful for monitoring physiological conditions |
AU2001296456A1 (en) | 2000-09-29 | 2002-04-08 | Healthetech, Inc. | Indirect calorimetry system |
IL138788A0 (en) | 2000-09-29 | 2001-10-31 | Falk Fish | Method and kit for the transdermal determination of analyte concentration in blood |
AU9658801A (en) | 2000-10-04 | 2002-04-15 | Insulet Corp | Data collection assembly for patient infusion system |
EP1339312B1 (en) | 2000-10-10 | 2006-01-04 | Microchips, Inc. | Microchip reservoir devices using wireless transmission of power and data |
US6537243B1 (en) | 2000-10-12 | 2003-03-25 | Abbott Laboratories | Device and method for obtaining interstitial fluid from a patient for diagnostic tests |
US20020133378A1 (en) | 2000-10-13 | 2002-09-19 | Mault James R. | System and method of integrated calorie management |
US6915347B2 (en) | 2000-10-17 | 2005-07-05 | Sun Microsystems, Inc. | Associating multiple display units in a grouped server environment |
WO2002047465A2 (en) | 2000-10-26 | 2002-06-20 | Healthetech, Inc. | Body supported activity and condition monitor |
TW537878B (en) | 2000-10-31 | 2003-06-21 | Trustmed Com Corp | Method for recording, tracking and analyzing blood sugar level, and device thereof |
US6695860B1 (en) | 2000-11-13 | 2004-02-24 | Isense Corp. | Transcutaneous sensor insertion device |
US20020083461A1 (en) | 2000-11-22 | 2002-06-27 | Hutcheson Stewart Douglas | Method and system for providing interactive services over a wireless communications network |
US6574510B2 (en) | 2000-11-30 | 2003-06-03 | Cardiac Pacemakers, Inc. | Telemetry apparatus and method for an implantable medical device |
WO2002043590A1 (en) | 2000-11-30 | 2002-06-06 | Arkray, Inc. | Measuring device equipped with comment input function |
US6645142B2 (en) | 2000-12-01 | 2003-11-11 | Optiscan Biomedical Corporation | Glucose monitoring instrument having network connectivity |
US6480744B2 (en) | 2000-12-04 | 2002-11-12 | Medtronic, Inc. | Implantable medical device telemetry control systems and methods of use |
JP2002174610A (en) | 2000-12-08 | 2002-06-21 | Nec Corp | Biosensor and liquid sample measurement method using biosensor |
US20020077766A1 (en) | 2000-12-11 | 2002-06-20 | Mault James R. | Remote temperature monitoring system |
JP4348082B2 (en) | 2000-12-11 | 2009-10-21 | レスメド・リミテッド | Device for judging the patient's situation after stroke onset |
TW492117B (en) | 2000-12-15 | 2002-06-21 | Acer Labs Inc | Substrate layout method and structure thereof for decreasing crosstalk between adjacent signals |
US20020074162A1 (en) | 2000-12-15 | 2002-06-20 | Bor-Ray Su | Substrate layout method and structure for reducing cross talk of adjacent signals |
US6665558B2 (en) * | 2000-12-15 | 2003-12-16 | Cardiac Pacemakers, Inc. | System and method for correlation of patient health information and implant device data |
US7052483B2 (en) | 2000-12-19 | 2006-05-30 | Animas Corporation | Transcutaneous inserter for low-profile infusion sets |
GB0030929D0 (en) | 2000-12-19 | 2001-01-31 | Inverness Medical Ltd | Analyte measurement |
DE60115707T2 (en) | 2000-12-21 | 2006-08-10 | Insulet Corp., Beverly | REMOTE CONTROL MEDICAL DEVICE |
US20020147135A1 (en) | 2000-12-21 | 2002-10-10 | Oliver Schnell | Method and device for producing an adapted travel treatment plan for administering a medicine in the event of a long-haul journey |
US8050625B2 (en) | 2000-12-22 | 2011-11-01 | Terahop Networks, Inc. | Wireless reader tags (WRTs) with sensor components in asset monitoring and tracking systems |
US6642015B2 (en) | 2000-12-29 | 2003-11-04 | Minimed Inc. | Hydrophilic polymeric material for coating biosensors |
US6512986B1 (en) | 2000-12-30 | 2003-01-28 | Lifescan, Inc. | Method for automated exception-based quality control compliance for point-of-care devices |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6800451B2 (en) | 2001-01-05 | 2004-10-05 | Sensors For Medicine And Science, Inc. | Detection of glucose in solutions also containing an alpha-hydroxy acid or a beta-diketone |
US6603770B2 (en) | 2001-01-16 | 2003-08-05 | Physical Optics Corporation | Apparatus and method for accessing a network |
US6970529B2 (en) | 2001-01-16 | 2005-11-29 | International Business Machines Corporation | Unified digital architecture |
US6627058B1 (en) | 2001-01-17 | 2003-09-30 | E. I. Du Pont De Nemours And Company | Thick film conductor composition for use in biosensors |
US20040197846A1 (en) | 2001-01-18 | 2004-10-07 | Linda Hockersmith | Determination of glucose sensitivity and a method to manipulate blood glucose concentration |
BR0206604A (en) | 2001-01-22 | 2004-02-17 | Hoffmann La Roche | Lancet device that has capillary action |
US6926670B2 (en) | 2001-01-22 | 2005-08-09 | Integrated Sensing Systems, Inc. | Wireless MEMS capacitive sensor for physiologic parameter measurement |
US6723046B2 (en) | 2001-01-29 | 2004-04-20 | Cybernet Systems Corporation | At-home health data management method and apparatus |
US6780871B2 (en) | 2001-01-29 | 2004-08-24 | Albany Medical College | Methods and compositions for treating addiction disorders |
US6927246B2 (en) | 2001-02-15 | 2005-08-09 | Medtronic Minimed, Inc. | Polymers functionalized with fluorescent boronate motifs and methods for making them |
AU2002248464A1 (en) | 2001-02-21 | 2002-09-12 | Medtronic Minimed, Inc. | Stabilized insulin formulations |
CA2434731C (en) | 2001-02-22 | 2010-01-26 | Insulet Corporation | Modular infusion device and method |
US6525330B2 (en) | 2001-02-28 | 2003-02-25 | Home Diagnostics, Inc. | Method of strip insertion detection |
US6541266B2 (en) * | 2001-02-28 | 2003-04-01 | Home Diagnostics, Inc. | Method for determining concentration of an analyte in a test strip |
US6968294B2 (en) | 2001-03-15 | 2005-11-22 | Koninklijke Philips Electronics N.V. | Automatic system for monitoring person requiring care and his/her caretaker |
US6611206B2 (en) | 2001-03-15 | 2003-08-26 | Koninklijke Philips Electronics N.V. | Automatic system for monitoring independent person requiring occasional assistance |
US6952603B2 (en) | 2001-03-16 | 2005-10-04 | Roche Diagnostics Operations, Inc. | Subcutaneous analyte sensor |
US6595929B2 (en) | 2001-03-30 | 2003-07-22 | Bodymedia, Inc. | System for monitoring health, wellness and fitness having a method and apparatus for improved measurement of heat flow |
US7041468B2 (en) | 2001-04-02 | 2006-05-09 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
US20070026440A1 (en) * | 2001-04-06 | 2007-02-01 | Broderick Patricia A | Identification, diagnosis, and treatment of neuropathologies, neurotoxicities, tumors, and brain and spinal cord injuries using electrodes with microvoltammetry |
US6694158B2 (en) | 2001-04-11 | 2004-02-17 | Motorola, Inc. | System using a portable detection device for detection of an analyte through body tissue |
US6454710B1 (en) | 2001-04-11 | 2002-09-24 | Motorola, Inc. | Devices and methods for monitoring an analyte |
US6983176B2 (en) | 2001-04-11 | 2006-01-03 | Rio Grande Medical Technologies, Inc. | Optically similar reference samples and related methods for multivariate calibration models used in optical spectroscopy |
US7916013B2 (en) | 2005-03-21 | 2011-03-29 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
GR1003802B (en) | 2001-04-17 | 2002-02-08 | Micrel �.�.�. ������� ��������� ��������������� ��������� | Tele-medicine system |
US6698269B2 (en) | 2001-04-27 | 2004-03-02 | Oceana Sensor Technologies, Inc. | Transducer in-situ testing apparatus and method |
US20030208409A1 (en) | 2001-04-30 | 2003-11-06 | Mault James R. | Method and apparatus for diet control |
US20040152961A1 (en) | 2001-05-07 | 2004-08-05 | Sven-Erik Carlson | Device for monitoring a patient |
US7395214B2 (en) | 2001-05-11 | 2008-07-01 | Craig P Shillingburg | Apparatus, device and method for prescribing, administering and monitoring a treatment regimen for a patient |
US6932894B2 (en) | 2001-05-15 | 2005-08-23 | Therasense, Inc. | Biosensor membranes composed of polymers containing heterocyclic nitrogens |
DE60214375T2 (en) | 2001-05-18 | 2007-08-30 | Polymer Technology Systems, Inc., Indianapolis | DEVICE FOR EXAMINING BODY FLUIDS WITH SOLVENTLY FIXED, PORTABLE TEST DEVICE |
US6549796B2 (en) | 2001-05-25 | 2003-04-15 | Lifescan, Inc. | Monitoring analyte concentration using minimally invasive devices |
JP4836354B2 (en) | 2001-06-05 | 2011-12-14 | アークレイ株式会社 | Data communication adapter |
US7025774B2 (en) | 2001-06-12 | 2006-04-11 | Pelikan Technologies, Inc. | Tissue penetration device |
US7179226B2 (en) | 2001-06-21 | 2007-02-20 | Animas Corporation | System and method for managing diabetes |
EP1403795A4 (en) | 2001-06-22 | 2007-08-01 | Arkray Inc | Information communication system |
WO2003000127A2 (en) | 2001-06-22 | 2003-01-03 | Cygnus, Inc. | Method for improving the performance of an analyte monitoring system |
US6737401B2 (en) | 2001-06-28 | 2004-05-18 | Metronic Minimed, Inc. | Methods of evaluating protein formulation stability and surfactant-stabilized insulin formulations derived therefrom |
US7044911B2 (en) | 2001-06-29 | 2006-05-16 | Philometron, Inc. | Gateway platform for biological monitoring and delivery of therapeutic compounds |
US20030040683A1 (en) | 2001-07-06 | 2003-02-27 | Peter Rule | Site selection for determining analyte concentration in living tissue |
US20030032868A1 (en) | 2001-07-09 | 2003-02-13 | Henning Graskov | Method and system for controlling data information between two portable apparatuses |
US20030208113A1 (en) | 2001-07-18 | 2003-11-06 | Mault James R | Closed loop glycemic index system |
US20030023182A1 (en) | 2001-07-26 | 2003-01-30 | Mault James R. | Respiratory connector for respiratory gas analysis |
US6702857B2 (en) | 2001-07-27 | 2004-03-09 | Dexcom, Inc. | Membrane for use with implantable devices |
US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
US6544212B2 (en) | 2001-07-31 | 2003-04-08 | Roche Diagnostics Corporation | Diabetes management system |
US7506046B2 (en) | 2001-07-31 | 2009-03-17 | Hewlett-Packard Development Company, L.P. | Network usage analysis system and method for updating statistical models |
US6505121B1 (en) * | 2001-08-01 | 2003-01-07 | Hewlett-Packard Company | Onboard vehicle navigation system |
WO2003014735A1 (en) | 2001-08-03 | 2003-02-20 | General Hospital Corporation | System, process and diagnostic arrangement establishing and monitoring medication doses for patients |
US6788965B2 (en) * | 2001-08-03 | 2004-09-07 | Sensys Medical, Inc. | Intelligent system for detecting errors and determining failure modes in noninvasive measurement of blood and tissue analytes |
JP3775263B2 (en) | 2001-08-10 | 2006-05-17 | ニプロ株式会社 | Recording medium and blood glucose measurement system using the recording medium |
EP1320322A1 (en) | 2001-08-20 | 2003-06-25 | Inverness Medical Limited | Wireless diabetes management devices and methods for using the same |
US20030039298A1 (en) | 2001-08-22 | 2003-02-27 | Lear Corporation | System and method of vehicle climate control |
EP1421588B1 (en) | 2001-08-29 | 2012-01-18 | MediaTek Inc. | Method and apparatus utilizing flash burst mode to improve processor performance |
JP3962250B2 (en) | 2001-08-29 | 2007-08-22 | 株式会社レアメタル | In vivo information detection system and tag device and relay device used therefor |
US6740072B2 (en) | 2001-09-07 | 2004-05-25 | Medtronic Minimed, Inc. | System and method for providing closed loop infusion formulation delivery |
US6827702B2 (en) | 2001-09-07 | 2004-12-07 | Medtronic Minimed, Inc. | Safety limits for closed-loop infusion pump control |
US6671554B2 (en) | 2001-09-07 | 2003-12-30 | Medtronic Minimed, Inc. | Electronic lead for a medical implant device, method of making same, and method and apparatus for inserting same |
US6915147B2 (en) | 2001-09-07 | 2005-07-05 | Medtronic Minimed, Inc. | Sensing apparatus and process |
WO2003022142A2 (en) | 2001-09-13 | 2003-03-20 | The Boeing Company | Method for transmitting vital health statistics to a remote location form an aircraft |
US6701270B1 (en) | 2001-09-20 | 2004-03-02 | Lsi Logic Corporation | Method for reliability testing leakage characteristics in an electronic circuit and a testing device for accomplishing the source |
US7258665B2 (en) | 2001-09-21 | 2007-08-21 | Ge Medical Systems Global Technology Company, Llc | High availability deployment of an off-site management system for digital cardiac electrocardiograms operating in an application service provider model |
US7052591B2 (en) | 2001-09-21 | 2006-05-30 | Therasense, Inc. | Electrodeposition of redox polymers and co-electrodeposition of enzymes by coordinative crosslinking |
US6830562B2 (en) | 2001-09-27 | 2004-12-14 | Unomedical A/S | Injector device for placing a subcutaneous infusion set |
US20050137480A1 (en) | 2001-10-01 | 2005-06-23 | Eckhard Alt | Remote control of implantable device through medical implant communication service band |
WO2003030731A2 (en) | 2001-10-09 | 2003-04-17 | Optiscan Biomedical Corporation | Method and apparatus for improving clinical accuracy of analyte measurements |
US20030081370A1 (en) | 2001-10-15 | 2003-05-01 | Haskell Donald K. | Apparatus and process for the control of electromagnetic fields on the surface of EMI filter capacitors |
US7854230B2 (en) | 2001-10-22 | 2010-12-21 | O.R. Solutions, Inc. | Heated medical instrument stand with surgical drape and method of detecting fluid and leaks in the stand tray |
US6923936B2 (en) | 2001-10-23 | 2005-08-02 | Medtronic Minimed, Inc. | Sterile device and method for producing same |
CN1267867C (en) | 2001-10-23 | 2006-08-02 | 西铁城时计株式会社 | Data collection system |
US6809507B2 (en) | 2001-10-23 | 2004-10-26 | Medtronic Minimed, Inc. | Implantable sensor electrodes and electronic circuitry |
AU2002356956A1 (en) | 2001-11-16 | 2003-06-10 | North Carolina State University | Biomedical electrochemical sensor array and method of fabrication |
US6708057B2 (en) * | 2001-11-20 | 2004-03-16 | Eresearchtechnology, Inc. | Method and system for processing electrocardiograms |
US20030175806A1 (en) | 2001-11-21 | 2003-09-18 | Peter Rule | Method and apparatus for improving the accuracy of alternative site analyte concentration measurements |
US20030105407A1 (en) | 2001-11-30 | 2003-06-05 | Pearce, Edwin M. | Disposable flow tube for respiratory gas analysis |
US7382405B2 (en) * | 2001-12-03 | 2008-06-03 | Nikon Corporation | Electronic apparatus having a user identification function and user identification method |
WO2003049609A1 (en) | 2001-12-07 | 2003-06-19 | Micronix, Inc. | Consolidated body fluid testing device and method |
US6957102B2 (en) | 2001-12-10 | 2005-10-18 | Medtronic Emergency Response Systems, Inc. | Enhanced interface for a medical device and a terminal |
TWI293363B (en) | 2001-12-11 | 2008-02-11 | Sensors For Med & Science Inc | High performance fluorescent optical sensor |
US7082334B2 (en) | 2001-12-19 | 2006-07-25 | Medtronic, Inc. | System and method for transmission of medical and like data from a patient to a dedicated internet website |
US7204823B2 (en) | 2001-12-19 | 2007-04-17 | Medtronic Minimed, Inc. | Medication delivery system and monitor |
US20030119457A1 (en) | 2001-12-19 | 2003-06-26 | Standke Randolph E. | Filter technique for increasing antenna isolation in portable communication devices |
US7729776B2 (en) | 2001-12-19 | 2010-06-01 | Cardiac Pacemakers, Inc. | Implantable medical device with two or more telemetry systems |
US7018568B2 (en) | 2001-12-20 | 2006-03-28 | Animas Technologies Llc | Highly catalytic screen-printing ink |
US7399277B2 (en) | 2001-12-27 | 2008-07-15 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
US20050027182A1 (en) | 2001-12-27 | 2005-02-03 | Uzair Siddiqui | System for monitoring physiological characteristics |
US7022072B2 (en) | 2001-12-27 | 2006-04-04 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
US20080255438A1 (en) | 2001-12-27 | 2008-10-16 | Medtronic Minimed, Inc. | System for monitoring physiological characteristics |
US7524309B2 (en) | 2001-12-28 | 2009-04-28 | Medtronic Minimed, Inc. | Variable length flexible conduit feeder |
US7060030B2 (en) | 2002-01-08 | 2006-06-13 | Cardiac Pacemakers, Inc. | Two-hop telemetry interface for medical device |
US6985870B2 (en) | 2002-01-11 | 2006-01-10 | Baxter International Inc. | Medication delivery system |
US6602909B1 (en) | 2002-01-23 | 2003-08-05 | Charles Ignatius Jarowski | Selected essential amino acid supplementation of dietary proteins to lower urinary urea and peak glucose levels |
US6980852B2 (en) | 2002-01-25 | 2005-12-27 | Subqiview Inc. | Film barrier dressing for intravascular tissue monitoring system |
US20030144711A1 (en) * | 2002-01-29 | 2003-07-31 | Neuropace, Inc. | Systems and methods for interacting with an implantable medical device |
US6985773B2 (en) * | 2002-02-07 | 2006-01-10 | Cardiac Pacemakers, Inc. | Methods and apparatuses for implantable medical device telemetry power management |
US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US9247901B2 (en) | 2003-08-22 | 2016-02-02 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US7613491B2 (en) | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
US20030212379A1 (en) | 2002-02-26 | 2003-11-13 | Bylund Adam David | Systems and methods for remotely controlling medication infusion and analyte monitoring |
EP1487519B1 (en) | 2002-02-26 | 2013-06-12 | TecPharma Licensing AG | Insertion device for an insertion set and method of using the same |
US6852104B2 (en) | 2002-02-28 | 2005-02-08 | Smiths Medical Md, Inc. | Programmable insulin pump |
US7468032B2 (en) | 2002-12-18 | 2008-12-23 | Cardiac Pacemakers, Inc. | Advanced patient management for identifying, displaying and assisting with correlating health-related data |
US7043305B2 (en) | 2002-03-06 | 2006-05-09 | Cardiac Pacemakers, Inc. | Method and apparatus for establishing context among events and optimizing implanted medical device performance |
EP1499231A4 (en) | 2002-03-08 | 2007-09-26 | Sensys Medical Inc | Compact apparatus for noninvasive measurement of glucose through near-infrared spectroscopy |
US6998247B2 (en) | 2002-03-08 | 2006-02-14 | Sensys Medical, Inc. | Method and apparatus using alternative site glucose determinations to calibrate and maintain noninvasive and implantable analyzers |
US6957107B2 (en) | 2002-03-13 | 2005-10-18 | Cardionet, Inc. | Method and apparatus for monitoring and communicating with an implanted medical device |
DE60334365D1 (en) | 2002-03-22 | 2010-11-11 | Animas Technologies Llc | INCREASED PERFORMANCE OF AN ANALYSIS MONITORING DEVICE |
GB0206792D0 (en) | 2002-03-22 | 2002-05-01 | Leuven K U Res & Dev | Normoglycemia |
US6936006B2 (en) | 2002-03-22 | 2005-08-30 | Novo Nordisk, A/S | Atraumatic insertion of a subcutaneous device |
US20040030531A1 (en) * | 2002-03-28 | 2004-02-12 | Honeywell International Inc. | System and method for automated monitoring, recognizing, supporting, and responding to the behavior of an actor |
GB2388898B (en) | 2002-04-02 | 2005-10-05 | Inverness Medical Ltd | Integrated sample testing meter |
US7563232B2 (en) | 2002-04-19 | 2009-07-21 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7410468B2 (en) | 2002-04-19 | 2008-08-12 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7232451B2 (en) | 2002-04-19 | 2007-06-19 | Pelikan Technologies, Inc. | Method and apparatus for penetrating tissue |
US7226461B2 (en) | 2002-04-19 | 2007-06-05 | Pelikan Technologies, Inc. | Method and apparatus for a multi-use body fluid sampling device with sterility barrier release |
US7052251B2 (en) | 2002-04-22 | 2006-05-30 | Medtronic Minimed, Inc. | Shape memory alloy wire driven positive displacement micropump with pulsatile output |
US20030232370A1 (en) | 2002-04-22 | 2003-12-18 | Trifiro Mark A. | Glucose sensor and uses thereof |
WO2003090614A1 (en) | 2002-04-25 | 2003-11-06 | Matsushita Electric Industrial Co., Ltd. | Dosage determination supporting device, injector, and health management supporting system |
US6810309B2 (en) | 2002-04-25 | 2004-10-26 | Visteon Global Technologies, Inc. | Vehicle personalization via biometric identification |
US6743635B2 (en) | 2002-04-25 | 2004-06-01 | Home Diagnostics, Inc. | System and methods for blood glucose sensing |
US6902207B2 (en) | 2002-05-01 | 2005-06-07 | Medtronic Minimed, Inc. | Self sealing disconnect device |
GB2388716B (en) | 2002-05-13 | 2004-10-20 | Splashpower Ltd | Improvements relating to contact-less power transfer |
US7226978B2 (en) | 2002-05-22 | 2007-06-05 | Dexcom, Inc. | Techniques to improve polyurethane membranes for implantable glucose sensors |
US6990317B2 (en) | 2002-05-28 | 2006-01-24 | Wireless Innovation | Interference resistant wireless sensor and control system |
US20040030581A1 (en) * | 2002-06-12 | 2004-02-12 | Samuel Leven | Heart monitoring device |
US7124027B1 (en) | 2002-07-11 | 2006-10-17 | Yazaki North America, Inc. | Vehicular collision avoidance system |
US20040010207A1 (en) | 2002-07-15 | 2004-01-15 | Flaherty J. Christopher | Self-contained, automatic transcutaneous physiologic sensing system |
JP2004054394A (en) | 2002-07-17 | 2004-02-19 | Toshiba Corp | Radio information processing system, radio information recording medium, radio information processor and communication method for radio information processing system |
US7470533B2 (en) | 2002-12-20 | 2008-12-30 | Acea Biosciences | Impedance based devices and methods for use in assays |
US7278983B2 (en) | 2002-07-24 | 2007-10-09 | Medtronic Minimed, Inc. | Physiological monitoring device for controlling a medication infusion device |
US8512276B2 (en) | 2002-07-24 | 2013-08-20 | Medtronic Minimed, Inc. | System for providing blood glucose measurements to an infusion device |
US6992580B2 (en) * | 2002-07-25 | 2006-01-31 | Motorola, Inc. | Portable communication device and corresponding method of operation |
JPWO2004014228A1 (en) | 2002-08-09 | 2005-11-24 | 松下電器産業株式会社 | Data measuring apparatus, healthcare data acquisition system, and healthcare data acquisition method |
WO2004015539A2 (en) | 2002-08-13 | 2004-02-19 | University Of Virginia Patent Foundation | Managing and processing self-monitoring blood glucose |
US7150975B2 (en) | 2002-08-19 | 2006-12-19 | Animas Technologies, Llc | Hydrogel composition for measuring glucose flux |
US7020508B2 (en) * | 2002-08-22 | 2006-03-28 | Bodymedia, Inc. | Apparatus for detecting human physiological and contextual information |
US20050118726A1 (en) | 2002-08-26 | 2005-06-02 | Schultz Jerome S. | System and method for detecting bioanalytes and method for producing a bioanalyte sensor |
ES2384558T3 (en) | 2002-09-11 | 2012-07-06 | Becton Dickinson And Company | Blood glucose monitoring including convenient visual presentation of averages and measurement values |
US7404796B2 (en) | 2004-03-01 | 2008-07-29 | Becton Dickinson And Company | System for determining insulin dose using carbohydrate to insulin ratio and insulin sensitivity factor |
US6991096B2 (en) | 2002-09-27 | 2006-01-31 | Medtronic Minimed, Inc. | Packaging system |
US6770729B2 (en) | 2002-09-30 | 2004-08-03 | Medtronic Minimed, Inc. | Polymer compositions containing bioactive agents and methods for their use |
US20040122530A1 (en) | 2002-09-30 | 2004-06-24 | Steffen Hansen | Indicating device with estimating feature |
US7192405B2 (en) | 2002-09-30 | 2007-03-20 | Becton, Dickinson And Company | Integrated lancet and bodily fluid sensor |
US6690276B1 (en) | 2002-10-02 | 2004-02-10 | Honeywell International, Inc | Method and apparatus for monitoring message acknowledgements in a security system |
JP4263568B2 (en) | 2002-10-07 | 2009-05-13 | 理想科学工業株式会社 | Stencil printing machine |
JP4599296B2 (en) | 2002-10-11 | 2010-12-15 | ベクトン・ディキンソン・アンド・カンパニー | System and method for initiating and maintaining continuous long-term control of the concentration of a substance in a patient's body using a feedback or model-based controller coupled to a single needle or multi-needle intradermal (ID) delivery device |
US7079977B2 (en) | 2002-10-15 | 2006-07-18 | Medtronic, Inc. | Synchronization and calibration of clocks for a medical device and calibrated clock |
US20040108226A1 (en) | 2002-10-28 | 2004-06-10 | Constantin Polychronakos | Continuous glucose quantification device and method |
US7233817B2 (en) | 2002-11-01 | 2007-06-19 | Brian Yen | Apparatus and method for pattern delivery of radiation and biological characteristic analysis |
US7381184B2 (en) | 2002-11-05 | 2008-06-03 | Abbott Diabetes Care Inc. | Sensor inserter assembly |
US7572237B2 (en) | 2002-11-06 | 2009-08-11 | Abbott Diabetes Care Inc. | Automatic biological analyte testing meter with integrated lancing device and methods of use |
GB0226648D0 (en) | 2002-11-15 | 2002-12-24 | Koninkl Philips Electronics Nv | Usage data harvesting |
JP2004234622A (en) | 2002-11-19 | 2004-08-19 | Seiko Instruments Inc | Living body information measuring system |
US20040100376A1 (en) | 2002-11-26 | 2004-05-27 | Kimberly-Clark Worldwide, Inc. | Healthcare monitoring system |
US7580395B2 (en) | 2002-11-29 | 2009-08-25 | Intermec Ip Corp. | Information gathering apparatus and method having multiple wireless communication options |
US7009511B2 (en) | 2002-12-17 | 2006-03-07 | Cardiac Pacemakers, Inc. | Repeater device for communications with an implantable medical device |
US7052472B1 (en) | 2002-12-18 | 2006-05-30 | Dsp Diabetes Sentry Products, Inc. | Systems and methods for detecting symptoms of hypoglycemia |
US20050038680A1 (en) | 2002-12-19 | 2005-02-17 | Mcmahon Kevin Lee | System and method for glucose monitoring |
US20040122353A1 (en) | 2002-12-19 | 2004-06-24 | Medtronic Minimed, Inc. | Relay device for transferring information between a sensor system and a fluid delivery system |
US7395117B2 (en) | 2002-12-23 | 2008-07-01 | Cardiac Pacemakers, Inc. | Implantable medical device having long-term wireless capabilities |
US7833151B2 (en) | 2002-12-26 | 2010-11-16 | Given Imaging Ltd. | In vivo imaging device with two imagers |
US6978182B2 (en) | 2002-12-27 | 2005-12-20 | Cardiac Pacemakers, Inc. | Advanced patient management system including interrogator/transceiver unit |
US8771183B2 (en) | 2004-02-17 | 2014-07-08 | Abbott Diabetes Care Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US7811231B2 (en) | 2002-12-31 | 2010-10-12 | Abbott Diabetes Care Inc. | Continuous glucose monitoring system and methods of use |
US7154398B2 (en) | 2003-01-06 | 2006-12-26 | Chen Thomas C H | Wireless communication and global location enabled intelligent health monitoring system |
US7396330B2 (en) | 2003-01-07 | 2008-07-08 | Triage Data Networks | Wireless, internet-based medical-diagnostic system |
US7018366B2 (en) | 2003-01-17 | 2006-03-28 | William Craig Easter | Vacuum assisted relief system (VARS) |
JP2004260786A (en) | 2003-02-05 | 2004-09-16 | Fujitsu Ltd | Antenna element, flat antenna, wiring board and communication system |
US20040172284A1 (en) | 2003-02-13 | 2004-09-02 | Roche Diagnostics Corporation | Information management system |
US20040164961A1 (en) | 2003-02-21 | 2004-08-26 | Debasis Bal | Method, system and computer product for continuously monitoring data sources for an event of interest |
US9872890B2 (en) * | 2003-03-19 | 2018-01-23 | Paul C. Davidson | Determining insulin dosing schedules and carbohydrate-to-insulin ratios in diabetic patients |
WO2004088304A2 (en) | 2003-04-01 | 2004-10-14 | Piet Moerman | Method and device for utilizing analyte levels to assist in the treatment of diabetes, insulin resistance and metabolic syndrome |
US20040199056A1 (en) | 2003-04-03 | 2004-10-07 | International Business Machines Corporation | Body monitoring using local area wireless interfaces |
US7587287B2 (en) | 2003-04-04 | 2009-09-08 | Abbott Diabetes Care Inc. | Method and system for transferring analyte test data |
US7134999B2 (en) | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US20040204868A1 (en) | 2003-04-09 | 2004-10-14 | Maynard John D. | Reduction of errors in non-invasive tissue sampling |
CN102811556A (en) | 2003-04-15 | 2012-12-05 | 医药及科学传感器公司 | Printed circuit board with integrated antenna and implantable sensor processing system with integrated printed circuit board antenna |
US20040225199A1 (en) | 2003-05-08 | 2004-11-11 | Evanyk Shane Walter | Advanced physiological monitoring systems and methods |
AU2003902187A0 (en) | 2003-05-08 | 2003-05-22 | Aimedics Pty Ltd | Patient monitor |
US7875293B2 (en) | 2003-05-21 | 2011-01-25 | Dexcom, Inc. | Biointerface membranes incorporating bioactive agents |
US20040249250A1 (en) | 2003-06-04 | 2004-12-09 | Mcgee Michael D. | System and apparatus for monitoring and prompting medical self-care events and communicating medical self-care status |
US20040253736A1 (en) | 2003-06-06 | 2004-12-16 | Phil Stout | Analytical device with prediction module and related methods |
US7258673B2 (en) | 2003-06-06 | 2007-08-21 | Lifescan, Inc | Devices, systems and methods for extracting bodily fluid and monitoring an analyte therein |
US20040249254A1 (en) | 2003-06-06 | 2004-12-09 | Joel Racchini | Devices, systems and methods for extracting bodily fluid and monitoring an analyte therein |
US20050016276A1 (en) | 2003-06-06 | 2005-01-27 | Palo Alto Sensor Technology Innovation | Frequency encoding of resonant mass sensors |
US7040139B2 (en) | 2003-06-10 | 2006-05-09 | Smiths Detection Inc. | Sensor arrangement |
US8066639B2 (en) | 2003-06-10 | 2011-11-29 | Abbott Diabetes Care Inc. | Glucose measuring device for use in personal area network |
US8460243B2 (en) | 2003-06-10 | 2013-06-11 | Abbott Diabetes Care Inc. | Glucose measuring module and insulin pump combination |
US20040254429A1 (en) | 2003-06-11 | 2004-12-16 | Health & Life Co., Ltd. | Data storage device for integrating data of several medical measuring instruments |
US20040254433A1 (en) | 2003-06-12 | 2004-12-16 | Bandis Steven D. | Sensor introducer system, apparatus and method |
US7155290B2 (en) | 2003-06-23 | 2006-12-26 | Cardiac Pacemakers, Inc. | Secure long-range telemetry for implantable medical device |
US7510564B2 (en) | 2003-06-27 | 2009-03-31 | Abbott Diabetes Care Inc. | Lancing device |
US7242981B2 (en) * | 2003-06-30 | 2007-07-10 | Codman Neuro Sciences Sárl | System and method for controlling an implantable medical device subject to magnetic field or radio frequency exposure |
US7722536B2 (en) * | 2003-07-15 | 2010-05-25 | Abbott Diabetes Care Inc. | Glucose measuring device integrated into a holster for a personal area network device |
WO2005007223A2 (en) | 2003-07-16 | 2005-01-27 | Sasha John | Programmable medical drug delivery systems and methods for delivery of multiple fluids and concentrations |
US7366556B2 (en) | 2003-12-05 | 2008-04-29 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US7424318B2 (en) | 2003-12-05 | 2008-09-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US7651596B2 (en) | 2005-04-08 | 2010-01-26 | Dexcom, Inc. | Cellulosic-based interference domain for an analyte sensor |
US7108778B2 (en) | 2003-07-25 | 2006-09-19 | Dexcom, Inc. | Electrochemical sensors including electrode systems with increased oxygen generation |
US7460898B2 (en) | 2003-12-05 | 2008-12-02 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
JP4708342B2 (en) | 2003-07-25 | 2011-06-22 | デックスコム・インコーポレーテッド | Oxygen augmentation membrane system for use in implantable devices |
JP2007500336A (en) | 2003-07-25 | 2007-01-11 | デックスコム・インコーポレーテッド | Electrode system for electrochemical sensors |
US7761130B2 (en) | 2003-07-25 | 2010-07-20 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US7467003B2 (en) | 2003-12-05 | 2008-12-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8282549B2 (en) | 2003-12-09 | 2012-10-09 | Dexcom, Inc. | Signal processing for continuous analyte sensor |
US8423113B2 (en) | 2003-07-25 | 2013-04-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20050176136A1 (en) | 2003-11-19 | 2005-08-11 | Dexcom, Inc. | Afinity domain for analyte sensor |
WO2005010756A2 (en) | 2003-07-25 | 2005-02-03 | Philips Intellectual Property & Standards Gmbh | Method and device for monitoring a system |
US8886273B2 (en) | 2003-08-01 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
US8275437B2 (en) | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8060173B2 (en) | 2003-08-01 | 2011-11-15 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8626257B2 (en) | 2003-08-01 | 2014-01-07 | Dexcom, Inc. | Analyte sensor |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US7925321B2 (en) * | 2003-08-01 | 2011-04-12 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US20070208245A1 (en) | 2003-08-01 | 2007-09-06 | Brauker James H | Transcutaneous analyte sensor |
US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8369919B2 (en) | 2003-08-01 | 2013-02-05 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7189341B2 (en) | 2003-08-15 | 2007-03-13 | Animas Technologies, Llc | Electrochemical sensor ink compositions, electrodes, and uses thereof |
US8346482B2 (en) | 2003-08-22 | 2013-01-01 | Fernandez Dennis S | Integrated biosensor and simulation system for diagnosis and therapy |
US8233959B2 (en) | 2003-08-22 | 2012-07-31 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
JP2005094282A (en) * | 2003-09-17 | 2005-04-07 | Renesas Technology Corp | Semiconductor integrated circuit for communication |
DE10343863A1 (en) | 2003-09-23 | 2005-04-14 | Roche Diagnostics Gmbh | Method and device for continuously monitoring the concentration of an analyte |
JP3612324B1 (en) | 2003-09-29 | 2005-01-19 | 株式会社日立製作所 | Blood glucose level display method and apparatus |
DE602004026763D1 (en) * | 2003-09-30 | 2010-06-02 | Roche Diagnostics Gmbh | SENSOR WITH IMPROVED BIOKOMPATIBILITY |
US8140168B2 (en) * | 2003-10-02 | 2012-03-20 | Medtronic, Inc. | External power source for an implantable medical device having an adjustable carrier frequency and system and method related therefore |
US7203549B2 (en) | 2003-10-02 | 2007-04-10 | Medtronic, Inc. | Medical device programmer with internal antenna and display |
US7490021B2 (en) | 2003-10-07 | 2009-02-10 | Hospira, Inc. | Method for adjusting pump screen brightness |
US7148803B2 (en) * | 2003-10-24 | 2006-12-12 | Symbol Technologies, Inc. | Radio frequency identification (RFID) based sensor networks |
US20050090607A1 (en) | 2003-10-28 | 2005-04-28 | Dexcom, Inc. | Silicone composition for biocompatible membrane |
WO2005041103A2 (en) | 2003-10-29 | 2005-05-06 | Novo Nordisk A/S | Medical advisory system |
US8373544B2 (en) * | 2003-10-29 | 2013-02-12 | Innovision Research & Technology Plc | RFID apparatus |
US20050096516A1 (en) | 2003-10-30 | 2005-05-05 | Orhan Soykan | Optical detector of organic analyte |
US6928380B2 (en) | 2003-10-30 | 2005-08-09 | International Business Machines Corporation | Thermal measurements of electronic devices during operation |
US7299082B2 (en) | 2003-10-31 | 2007-11-20 | Abbott Diabetes Care, Inc. | Method of calibrating an analyte-measurement device, and associated methods, devices and systems |
ES2739529T3 (en) | 2003-11-06 | 2020-01-31 | Lifescan Inc | Drug administration pen with event notification means |
US7419573B2 (en) | 2003-11-06 | 2008-09-02 | 3M Innovative Properties Company | Circuit for electrochemical sensor strip |
WO2005051170A2 (en) | 2003-11-19 | 2005-06-09 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
US20050113648A1 (en) | 2003-11-24 | 2005-05-26 | Soohyun Yang | Bidirectional monitoring system capable of a medical diagnosis and a commercial broadcast |
US20050113886A1 (en) | 2003-11-24 | 2005-05-26 | Fischell David R. | Implantable medical system with long range telemetry |
US7496392B2 (en) | 2003-11-26 | 2009-02-24 | Becton, Dickinson And Company | Fiber optic device for sensing analytes |
US20050148003A1 (en) | 2003-11-26 | 2005-07-07 | Steven Keith | Methods of correcting a luminescence value, and methods of determining a corrected analyte concentration |
US7787923B2 (en) | 2003-11-26 | 2010-08-31 | Becton, Dickinson And Company | Fiber optic device for sensing analytes and method of making same |
US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
US20080200788A1 (en) | 2006-10-04 | 2008-08-21 | Dexcorn, Inc. | Analyte sensor |
US8425417B2 (en) | 2003-12-05 | 2013-04-23 | Dexcom, Inc. | Integrated device for continuous in vivo analyte detection and simultaneous control of an infusion device |
DE602004029092D1 (en) | 2003-12-05 | 2010-10-21 | Dexcom Inc | CALIBRATION METHODS FOR A CONTINUOUSLY WORKING ANALYTIC SENSOR |
US20080197024A1 (en) | 2003-12-05 | 2008-08-21 | Dexcom, Inc. | Analyte sensor |
US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
US8364230B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
US8425416B2 (en) | 2006-10-04 | 2013-04-23 | Dexcom, Inc. | Analyte sensor |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8532730B2 (en) | 2006-10-04 | 2013-09-10 | Dexcom, Inc. | Analyte sensor |
ES2646312T3 (en) | 2003-12-08 | 2017-12-13 | Dexcom, Inc. | Systems and methods to improve electromechanical analyte sensors |
US20050137471A1 (en) | 2003-12-18 | 2005-06-23 | Hans-Peter Haar | Continuous glucose monitoring device |
US7384397B2 (en) | 2003-12-30 | 2008-06-10 | Medtronic Minimed, Inc. | System and method for sensor recalibration |
GB2409951A (en) | 2004-01-08 | 2005-07-13 | Remote Diagnostic Technologies | Wireless local area network of medical sensors |
US7637868B2 (en) | 2004-01-12 | 2009-12-29 | Dexcom, Inc. | Composite material for implantable device |
US20050182451A1 (en) | 2004-01-12 | 2005-08-18 | Adam Griffin | Implantable device with improved radio frequency capabilities |
CN1910600B (en) * | 2004-01-23 | 2011-12-14 | 株式会社半导体能源研究所 | ID label, ID card, and ID tag |
PL1709750T3 (en) | 2004-01-27 | 2015-03-31 | Altivera L L C | Diagnostic radio frequency identification sensors and applications thereof |
US8165651B2 (en) | 2004-02-09 | 2012-04-24 | Abbott Diabetes Care Inc. | Analyte sensor, and associated system and method employing a catalytic agent |
US7699964B2 (en) | 2004-02-09 | 2010-04-20 | Abbott Diabetes Care Inc. | Membrane suitable for use in an analyte sensor, analyte sensor, and associated method |
US7364592B2 (en) | 2004-02-12 | 2008-04-29 | Dexcom, Inc. | Biointerface membrane with macro-and micro-architecture |
US20060154642A1 (en) | 2004-02-20 | 2006-07-13 | Scannell Robert F Jr | Medication & health, environmental, and security monitoring, alert, intervention, information and network system with associated and supporting apparatuses |
JP3590053B1 (en) | 2004-02-24 | 2004-11-17 | 株式会社日立製作所 | Blood glucose measurement device |
US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US7228182B2 (en) | 2004-03-15 | 2007-06-05 | Cardiac Pacemakers, Inc. | Cryptographic authentication for telemetry with an implantable medical device |
US7831828B2 (en) | 2004-03-15 | 2010-11-09 | Cardiac Pacemakers, Inc. | System and method for securely authenticating a data exchange session with an implantable medical device |
JP5051767B2 (en) | 2004-03-22 | 2012-10-17 | ボディーメディア インコーポレイテッド | Device for monitoring human condition parameters |
EP1735729A2 (en) | 2004-03-26 | 2006-12-27 | Novo Nordisk A/S | Device for displaying data relevant for a diabetic patient |
US20050221504A1 (en) | 2004-04-01 | 2005-10-06 | Petruno Patrick T | Optoelectronic rapid diagnostic test system |
US6971274B2 (en) | 2004-04-02 | 2005-12-06 | Sierra Instruments, Inc. | Immersible thermal mass flow meter |
US20060258918A1 (en) | 2004-04-14 | 2006-11-16 | Oculir, Inc. | Combination Analyte Measurement Device and Method of Use |
US20070135697A1 (en) | 2004-04-19 | 2007-06-14 | Therasense, Inc. | Method and apparatus for providing sensor guard for data monitoring and detection systems |
US7324850B2 (en) * | 2004-04-29 | 2008-01-29 | Cardiac Pacemakers, Inc. | Method and apparatus for communication between a handheld programmer and an implantable medical device |
US8277713B2 (en) | 2004-05-03 | 2012-10-02 | Dexcom, Inc. | Implantable analyte sensor |
US20050245799A1 (en) | 2004-05-03 | 2005-11-03 | Dexcom, Inc. | Implantable analyte sensor |
US7651845B2 (en) | 2004-05-13 | 2010-01-26 | The Regents Of The University Of California | Method and apparatus for glucose control and insulin dosing for diabetics |
US7125382B2 (en) | 2004-05-20 | 2006-10-24 | Digital Angel Corporation | Embedded bio-sensor system |
US20050261660A1 (en) | 2004-05-24 | 2005-11-24 | Choi Soo B | Method for controlling insulin pump using Bluetooth protocol |
GB0411884D0 (en) | 2004-05-28 | 2004-06-30 | Koninkl Philips Electronics Nv | Bitstream controlled reference signal generation for a sigma-delta modulator |
WO2005119555A2 (en) | 2004-06-01 | 2005-12-15 | Lifescan, Inc. | Methods and systems of automating medical device data management |
US7289855B2 (en) | 2004-06-09 | 2007-10-30 | Medtronic, Inc. | Implantable medical device package antenna |
US7283867B2 (en) | 2004-06-10 | 2007-10-16 | Ndi Medical, Llc | Implantable system and methods for acquisition and processing of electrical signals from muscles and/or nerves and/or central nervous system tissue |
US20070100222A1 (en) | 2004-06-14 | 2007-05-03 | Metronic Minimed, Inc. | Analyte sensing apparatus for hospital use |
US7565197B2 (en) | 2004-06-18 | 2009-07-21 | Medtronic, Inc. | Conditional requirements for remote medical device programming |
US7623988B2 (en) | 2004-06-23 | 2009-11-24 | Cybiocare Inc. | Method and apparatus for the monitoring of clinical states |
US7221977B1 (en) | 2004-06-25 | 2007-05-22 | Pacesetter, Inc. | Method and apparatus for measuring battery depletion in implantable medical devices |
DE102004031092A1 (en) | 2004-06-28 | 2006-01-12 | Giesecke & Devrient Gmbh | transponder unit |
US20060001551A1 (en) | 2004-06-30 | 2006-01-05 | Ulrich Kraft | Analyte monitoring system with wireless alarm |
US20060001538A1 (en) | 2004-06-30 | 2006-01-05 | Ulrich Kraft | Methods of monitoring the concentration of an analyte |
US20060036187A1 (en) | 2004-06-30 | 2006-02-16 | Hester Vos | Devices, systems and methods for extracting bodily fluid and monitoring an analyte therein |
MXPA06014896A (en) | 2004-07-01 | 2007-08-20 | Vivomedical Inc | Non-invasive glucose measurement. |
US20060015020A1 (en) | 2004-07-06 | 2006-01-19 | Dexcom, Inc. | Systems and methods for manufacture of an analyte-measuring device including a membrane system |
WO2006127694A2 (en) | 2004-07-13 | 2006-11-30 | Dexcom, Inc. | Analyte sensor |
US20080242961A1 (en) | 2004-07-13 | 2008-10-02 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7946984B2 (en) | 2004-07-13 | 2011-05-24 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7783333B2 (en) | 2004-07-13 | 2010-08-24 | Dexcom, Inc. | Transcutaneous medical device with variable stiffness |
US8886272B2 (en) | 2004-07-13 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
US8565848B2 (en) | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8452368B2 (en) | 2004-07-13 | 2013-05-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060016700A1 (en) | 2004-07-13 | 2006-01-26 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7344500B2 (en) | 2004-07-27 | 2008-03-18 | Medtronic Minimed, Inc. | Sensing system with auxiliary display |
US7261691B1 (en) | 2004-08-02 | 2007-08-28 | Kwabena Asomani | Personalized emergency medical monitoring and transmission system |
US8313433B2 (en) | 2004-08-06 | 2012-11-20 | Medtronic Minimed, Inc. | Medical data management system and process |
US20060058602A1 (en) | 2004-08-17 | 2006-03-16 | Kwiatkowski Krzysztof C | Interstitial fluid analyzer |
US7291107B2 (en) | 2004-08-26 | 2007-11-06 | Roche Diagnostics Operations, Inc. | Insulin bolus recommendation system |
CN101091114A (en) | 2004-08-31 | 2007-12-19 | 生命扫描苏格兰有限公司 | Method of manufacturing an auto-calibrating sensor |
EP1799101A4 (en) | 2004-09-02 | 2008-11-19 | Proteus Biomedical Inc | Methods and apparatus for tissue activation and monitoring |
US20080312859A1 (en) | 2004-09-03 | 2008-12-18 | Novo Nordisk A/S | Method of Calibrating a System for Measuring the Concentration of Substances in Body and an Apparatus for Exercising the Method |
EP1635508A1 (en) | 2004-09-08 | 2006-03-15 | Koninklijke Philips Electronics N.V. | Secure pairing for wireless communications devices |
EP1794695A2 (en) | 2004-09-23 | 2007-06-13 | Novo Nordisk A/S | Device for self-care support |
US8500054B2 (en) | 2004-09-27 | 2013-08-06 | Deka Products Limited Partnership | Infusion set improvements |
US10201305B2 (en) | 2004-11-02 | 2019-02-12 | Medtronic, Inc. | Apparatus for data retention in an implantable medical device |
US7237712B2 (en) | 2004-12-01 | 2007-07-03 | Alfred E. Mann Foundation For Scientific Research | Implantable device and communication integrated circuit implementable therein |
ATE545361T1 (en) | 2004-12-13 | 2012-03-15 | Koninkl Philips Electronics Nv | MOBILE MONITORING |
US7461192B2 (en) | 2004-12-15 | 2008-12-02 | Rambus Inc. | Interface for bridging out-of-band information and preventing false presence detection of terminating devices |
US20100331646A1 (en) | 2009-06-30 | 2010-12-30 | Abbott Diabetes Care Inc. | Health Management Devices and Methods |
US7731657B2 (en) | 2005-08-30 | 2010-06-08 | Abbott Diabetes Care Inc. | Analyte sensor introducer and methods of use |
US20070027381A1 (en) | 2005-07-29 | 2007-02-01 | Therasense, Inc. | Inserter and methods of use |
US7883464B2 (en) | 2005-09-30 | 2011-02-08 | Abbott Diabetes Care Inc. | Integrated transmitter unit and sensor introducer mechanism and methods of use |
US9398882B2 (en) | 2005-09-30 | 2016-07-26 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor and data processing device |
US8512243B2 (en) | 2005-09-30 | 2013-08-20 | Abbott Diabetes Care Inc. | Integrated introducer and transmitter assembly and methods of use |
US20060166629A1 (en) | 2005-01-24 | 2006-07-27 | Therasense, Inc. | Method and apparatus for providing EMC Class-B compliant RF transmitter for data monitoring an detection systems |
US20060173260A1 (en) | 2005-01-31 | 2006-08-03 | Gmms Ltd | System, device and method for diabetes treatment and monitoring |
US7547281B2 (en) | 2005-02-01 | 2009-06-16 | Medtronic Minimed, Inc. | Algorithm sensor augmented bolus estimator for semi-closed loop infusion system |
US7545272B2 (en) | 2005-02-08 | 2009-06-09 | Therasense, Inc. | RF tag on test strips, test strip vials and boxes |
KR100638727B1 (en) | 2005-02-28 | 2006-10-30 | 삼성전기주식회사 | Concurrent transceiver for zigbee and bluetooth |
US20060200112A1 (en) | 2005-03-01 | 2006-09-07 | Paul Patrick J | Medical infusion device having a refillable reservoir and switch for controlling fluid direction |
US20090076360A1 (en) | 2007-09-13 | 2009-03-19 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060202805A1 (en) | 2005-03-14 | 2006-09-14 | Alfred E. Mann Foundation For Scientific Research | Wireless acquisition and monitoring system |
EP1859279A4 (en) | 2005-03-15 | 2009-12-30 | Entelos Inc | Apparatus and method for computer modeling type 1 diabetes |
WO2006102412A2 (en) | 2005-03-21 | 2006-09-28 | Abbott Diabetes Care, Inc. | Method and system for providing integrated medication infusion and analyte monitoring system |
US7889069B2 (en) * | 2005-04-01 | 2011-02-15 | Codman & Shurtleff, Inc. | Wireless patient monitoring system |
US8204565B2 (en) * | 2005-04-04 | 2012-06-19 | University Of Iowa Research Foundation | Reagentless optical analyte detection system |
WO2006113618A1 (en) | 2005-04-15 | 2006-10-26 | Dexcom, Inc. | Analyte sensing biointerface |
US7270633B1 (en) | 2005-04-22 | 2007-09-18 | Cardiac Pacemakers, Inc. | Ambulatory repeater for use in automated patient care and method thereof |
DE102005019306B4 (en) | 2005-04-26 | 2011-09-01 | Disetronic Licensing Ag | Energy-optimized data transmission of a medical device |
GB2425601B (en) | 2005-04-26 | 2008-01-30 | Bio Nano Sensium Technologies | Sensor configuration |
US20060247985A1 (en) | 2005-04-29 | 2006-11-02 | Therasense, Inc. | Method and system for monitoring consumable item usage and providing replenishment thereof |
US8112240B2 (en) | 2005-04-29 | 2012-02-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing leak detection in data monitoring and management systems |
US8700157B2 (en) | 2005-04-29 | 2014-04-15 | Medtronic, Inc. | Telemetry head programmer for implantable medical device and system and method |
US9233203B2 (en) | 2005-05-06 | 2016-01-12 | Medtronic Minimed, Inc. | Medical needles for damping motion |
US7604178B2 (en) | 2005-05-11 | 2009-10-20 | Intelleflex Corporation | Smart tag activation |
EP1881786B1 (en) | 2005-05-13 | 2017-11-15 | Trustees of Boston University | Fully automated control system for type 1 diabetes |
US7541935B2 (en) | 2005-05-19 | 2009-06-02 | Proacticare Llc | System and methods for monitoring caregiver performance |
US20060272652A1 (en) | 2005-06-03 | 2006-12-07 | Medtronic Minimed, Inc. | Virtual patient software system for educating and treating individuals with diabetes |
US20070033074A1 (en) | 2005-06-03 | 2007-02-08 | Medtronic Minimed, Inc. | Therapy management system |
US20070016449A1 (en) | 2005-06-29 | 2007-01-18 | Gary Cohen | Flexible glucose analysis using varying time report deltas and configurable glucose target ranges |
AU2006269374C1 (en) | 2005-07-12 | 2010-03-25 | Massachusetts Institute Of Technology | Wireless non-radiative energy transfer |
WO2007007459A1 (en) | 2005-07-12 | 2007-01-18 | Omron Healthcare Co., Ltd. | Biochemical measuring instrument for measuring information about component of living body accurately |
US7413124B2 (en) | 2005-07-19 | 2008-08-19 | 3M Innovative Properties Company | RFID reader supporting one-touch search functionality |
US20070093786A1 (en) | 2005-08-16 | 2007-04-26 | Medtronic Minimed, Inc. | Watch controller for a medical device |
US20070060869A1 (en) * | 2005-08-16 | 2007-03-15 | Tolle Mike C V | Controller device for an infusion pump |
EP1758039A1 (en) * | 2005-08-27 | 2007-02-28 | Roche Diagnostics GmbH | Communication adaptor for portable medical or therapeutical devices |
US7264985B2 (en) | 2005-08-31 | 2007-09-04 | Freescale Semiconductor, Inc. | Passive elements in MRAM embedded integrated circuits |
US20070053341A1 (en) | 2005-09-06 | 2007-03-08 | Lizzi Ronald S | System and method for synchronizing companion electronic devices |
US7725148B2 (en) * | 2005-09-23 | 2010-05-25 | Medtronic Minimed, Inc. | Sensor with layered electrodes |
US9072476B2 (en) | 2005-09-23 | 2015-07-07 | Medtronic Minimed, Inc. | Flexible sensor apparatus |
US7756561B2 (en) | 2005-09-30 | 2010-07-13 | Abbott Diabetes Care Inc. | Method and apparatus for providing rechargeable power in data monitoring and management systems |
US9521968B2 (en) | 2005-09-30 | 2016-12-20 | Abbott Diabetes Care Inc. | Analyte sensor retention mechanism and methods of use |
US7701052B2 (en) | 2005-10-21 | 2010-04-20 | E. I. Du Pont De Nemours And Company | Power core devices |
US20090054747A1 (en) | 2005-10-31 | 2009-02-26 | Abbott Diabetes Care, Inc. | Method and system for providing analyte sensor tester isolation |
US7766829B2 (en) | 2005-11-04 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and system for providing basal profile modification in analyte monitoring and management systems |
EP3064236B1 (en) | 2005-11-08 | 2020-02-05 | Bigfoot Biomedical, Inc. | Method and system for manual and autonomous control of an infusion pump |
US20070173706A1 (en) | 2005-11-11 | 2007-07-26 | Isense Corporation | Method and apparatus for insertion of a sensor |
WO2007062173A1 (en) | 2005-11-22 | 2007-05-31 | Vocollect Healthcare Systems, Inc. | Advanced diabetes management system (adms) |
EP1968432A4 (en) | 2005-12-28 | 2009-10-21 | Abbott Diabetes Care Inc | Medical device insertion |
US8515518B2 (en) | 2005-12-28 | 2013-08-20 | Abbott Diabetes Care Inc. | Analyte monitoring |
US8102789B2 (en) | 2005-12-29 | 2012-01-24 | Medtronic, Inc. | System and method for synchronous wireless communication with a medical device |
US20070173712A1 (en) | 2005-12-30 | 2007-07-26 | Medtronic Minimed, Inc. | Method of and system for stabilization of sensors |
US7574266B2 (en) | 2006-01-19 | 2009-08-11 | Medtronic, Inc. | System and method for telemetry with an implantable medical device |
US20070179349A1 (en) | 2006-01-19 | 2007-08-02 | Hoyme Kenneth P | System and method for providing goal-oriented patient management based upon comparative population data analysis |
US7872574B2 (en) | 2006-02-01 | 2011-01-18 | Innovation Specialists, Llc | Sensory enhancement systems and methods in personal electronic devices |
DE602007013723D1 (en) | 2006-02-09 | 2011-05-19 | Deka Products Lp | SYSTEMS FOR DISPENSING FLUIDS IN PATCH SIZE |
EP1993637A2 (en) | 2006-02-15 | 2008-11-26 | Medingo Ltd. | Systems and methods for sensing analyte and dispensing therapeutic fluid |
US7826879B2 (en) | 2006-02-28 | 2010-11-02 | Abbott Diabetes Care Inc. | Analyte sensors and methods of use |
US7981034B2 (en) | 2006-02-28 | 2011-07-19 | Abbott Diabetes Care Inc. | Smart messages and alerts for an infusion delivery and management system |
US7576657B2 (en) | 2006-03-22 | 2009-08-18 | Symbol Technologies, Inc. | Single frequency low power RFID device |
US9392969B2 (en) | 2008-08-31 | 2016-07-19 | Abbott Diabetes Care Inc. | Closed loop control and signal attenuation detection |
US7653425B2 (en) | 2006-08-09 | 2010-01-26 | Abbott Diabetes Care Inc. | Method and system for providing calibration of an analyte sensor in an analyte monitoring system |
US8140312B2 (en) | 2007-05-14 | 2012-03-20 | Abbott Diabetes Care Inc. | Method and system for determining analyte levels |
US7801582B2 (en) | 2006-03-31 | 2010-09-21 | Abbott Diabetes Care Inc. | Analyte monitoring and management system and methods therefor |
US8226891B2 (en) | 2006-03-31 | 2012-07-24 | Abbott Diabetes Care Inc. | Analyte monitoring devices and methods therefor |
US7618369B2 (en) | 2006-10-02 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for dynamically updating calibration parameters for an analyte sensor |
US8473022B2 (en) | 2008-01-31 | 2013-06-25 | Abbott Diabetes Care Inc. | Analyte sensor with time lag compensation |
US8224415B2 (en) | 2009-01-29 | 2012-07-17 | Abbott Diabetes Care Inc. | Method and device for providing offset model based calibration for analyte sensor |
US7620438B2 (en) | 2006-03-31 | 2009-11-17 | Abbott Diabetes Care Inc. | Method and system for powering an electronic device |
ATE449518T1 (en) * | 2006-04-20 | 2009-12-15 | Lifescan Scotland Ltd | METHOD FOR SENDING DATA IN A BLOOD GLUCOSE SYSTEM AND CORRESPONDING BLOOD GLUCOSE SYSTEM |
US7359837B2 (en) | 2006-04-27 | 2008-04-15 | Medtronic, Inc. | Peak data retention of signal data in an implantable medical device |
US20070253021A1 (en) | 2006-04-28 | 2007-11-01 | Medtronic Minimed, Inc. | Identification of devices in a medical device network and wireless data communication techniques utilizing device identifiers |
US20070258395A1 (en) | 2006-04-28 | 2007-11-08 | Medtronic Minimed, Inc. | Wireless data communication protocols for a medical device network |
US20070255126A1 (en) | 2006-04-28 | 2007-11-01 | Moberg Sheldon B | Data communication in networked fluid infusion systems |
US8380300B2 (en) | 2006-04-28 | 2013-02-19 | Medtronic, Inc. | Efficacy visualization |
US8135352B2 (en) * | 2006-05-02 | 2012-03-13 | 3M Innovative Properties Company | Telecommunication enclosure monitoring system |
GB0608829D0 (en) | 2006-05-04 | 2006-06-14 | Husheer Shamus L G | In-situ measurement of physical parameters |
US7496852B2 (en) | 2006-05-16 | 2009-02-24 | International Business Machines Corporation | Graphically manipulating a database |
DE102006023213B3 (en) * | 2006-05-17 | 2007-09-27 | Siemens Ag | Sensor operating method, involves detecting recording and evaluation device during order and non-order functions of monitoring device in check mode, and watching occurrence of results in mode by sensor, which automatically leaves mode |
DE102006025485B4 (en) * | 2006-05-30 | 2008-03-20 | Polylc Gmbh & Co. Kg | Antenna arrangement and its use |
WO2007143225A2 (en) | 2006-06-07 | 2007-12-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and method |
US8098159B2 (en) * | 2006-06-09 | 2012-01-17 | Intelleflex Corporation | RF device comparing DAC output to incoming signal for selectively performing an action |
US7796038B2 (en) | 2006-06-12 | 2010-09-14 | Intelleflex Corporation | RFID sensor tag with manual modes and functions |
WO2007149949A1 (en) | 2006-06-20 | 2007-12-27 | Rain Bird Corporation | Sensor device for interrupting irrigation |
US20070299617A1 (en) | 2006-06-27 | 2007-12-27 | Willis John P | Biofouling self-compensating biosensor |
US20080004601A1 (en) | 2006-06-28 | 2008-01-03 | Abbott Diabetes Care, Inc. | Analyte Monitoring and Therapy Management System and Methods Therefor |
US9119582B2 (en) | 2006-06-30 | 2015-09-01 | Abbott Diabetes Care, Inc. | Integrated analyte sensor and infusion device and methods therefor |
US20090105571A1 (en) | 2006-06-30 | 2009-04-23 | Abbott Diabetes Care, Inc. | Method and System for Providing Data Communication in Data Management Systems |
US7680469B2 (en) * | 2006-07-06 | 2010-03-16 | Hewlett-Packard Development Company, L.P. | Electronic device power management system and method |
GB0616331D0 (en) | 2006-08-16 | 2006-09-27 | Innovision Res & Tech Plc | Near Field RF Communicators And Near Field Communications Enabled Devices |
US20090256572A1 (en) * | 2008-04-14 | 2009-10-15 | Mcdowell Andrew F | Tuning Low-Inductance Coils at Low Frequencies |
US7769456B2 (en) * | 2006-09-01 | 2010-08-03 | Cardiac Pacemakers, Inc. | Frequency-agile system for telemetry with implantable device |
US20080057484A1 (en) * | 2006-09-05 | 2008-03-06 | Shinichi Miyata | Event-driven method for tutoring a user in the determination of an analyte in a bodily fluid sample |
US20080058678A1 (en) | 2006-09-05 | 2008-03-06 | Shinichi Miyata | Kit for the determination of an analyte in a bodily fluid sample that includes a meter with a display-based tutorial module |
US9056165B2 (en) | 2006-09-06 | 2015-06-16 | Medtronic Minimed, Inc. | Intelligent therapy recommendation algorithm and method of using the same |
US20080071328A1 (en) * | 2006-09-06 | 2008-03-20 | Medtronic, Inc. | Initiating medical system communications |
US7696941B2 (en) | 2006-09-11 | 2010-04-13 | Elster Electricity, Llc | Printed circuit notch antenna |
DE102006043484B4 (en) * | 2006-09-15 | 2019-11-28 | Infineon Technologies Ag | Fuse structure and method for producing the same |
US7779332B2 (en) | 2006-09-25 | 2010-08-17 | Alfred E. Mann Foundation For Scientific Research | Rotationally invariant non-coherent burst coding |
CA2701006C (en) | 2006-09-27 | 2016-07-12 | University Of Connecticut | Implantable biosensor and methods of use thereof |
US7831287B2 (en) | 2006-10-04 | 2010-11-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8447376B2 (en) | 2006-10-04 | 2013-05-21 | Dexcom, Inc. | Analyte sensor |
US8562528B2 (en) | 2006-10-04 | 2013-10-22 | Dexcom, Inc. | Analyte sensor |
US8449464B2 (en) | 2006-10-04 | 2013-05-28 | Dexcom, Inc. | Analyte sensor |
US8478377B2 (en) | 2006-10-04 | 2013-07-02 | Dexcom, Inc. | Analyte sensor |
US8275438B2 (en) | 2006-10-04 | 2012-09-25 | Dexcom, Inc. | Analyte sensor |
US8298142B2 (en) | 2006-10-04 | 2012-10-30 | Dexcom, Inc. | Analyte sensor |
US8233456B1 (en) | 2006-10-16 | 2012-07-31 | Marvell International Ltd. | Power save mechanisms for dynamic ad-hoc networks |
US20080092638A1 (en) | 2006-10-19 | 2008-04-24 | Bayer Healthcare Llc | Wireless analyte monitoring system |
US8126728B2 (en) * | 2006-10-24 | 2012-02-28 | Medapps, Inc. | Systems and methods for processing and transmittal of medical data through an intermediary device |
EP2106238A4 (en) | 2006-10-26 | 2011-03-09 | Abbott Diabetes Care Inc | Method, system and computer program product for real-time detection of sensitivity decline in analyte sensors |
EP1918837A1 (en) * | 2006-10-31 | 2008-05-07 | F. Hoffmann-La Roche AG | Method for processing a chronological sequence of measurements of a time dependent parameter |
US20080119705A1 (en) | 2006-11-17 | 2008-05-22 | Medtronic Minimed, Inc. | Systems and Methods for Diabetes Management Using Consumer Electronic Devices |
US20080139910A1 (en) | 2006-12-06 | 2008-06-12 | Metronic Minimed, Inc. | Analyte sensor and method of using the same |
KR100833511B1 (en) * | 2006-12-08 | 2008-05-29 | 한국전자통신연구원 | Passive tag with volatile memory |
WO2008071218A1 (en) | 2006-12-14 | 2008-06-19 | Egomedical Swiss Ag | Monitoring device |
US8120493B2 (en) * | 2006-12-20 | 2012-02-21 | Intel Corporation | Direct communication in antenna devices |
US20080154513A1 (en) | 2006-12-21 | 2008-06-26 | University Of Virginia Patent Foundation | Systems, Methods and Computer Program Codes for Recognition of Patterns of Hyperglycemia and Hypoglycemia, Increased Glucose Variability, and Ineffective Self-Monitoring in Diabetes |
US20080161666A1 (en) | 2006-12-29 | 2008-07-03 | Abbott Diabetes Care, Inc. | Analyte devices and methods |
US7946985B2 (en) | 2006-12-29 | 2011-05-24 | Medtronic Minimed, Inc. | Method and system for providing sensor redundancy |
WO2008089184A2 (en) | 2007-01-15 | 2008-07-24 | Deka Products Limited Partnership | Device and method for food management |
US8098160B2 (en) * | 2007-01-22 | 2012-01-17 | Cisco Technology, Inc. | Method and system for remotely provisioning and/or configuring a device |
US10154804B2 (en) | 2007-01-31 | 2018-12-18 | Medtronic Minimed, Inc. | Model predictive method and system for controlling and supervising insulin infusion |
US8808515B2 (en) | 2007-01-31 | 2014-08-19 | Abbott Diabetes Care Inc. | Heterocyclic nitrogen containing polymers coated analyte monitoring device and methods of use |
US9597019B2 (en) | 2007-02-09 | 2017-03-21 | Lifescan, Inc. | Method of ensuring date and time on a test meter is accurate |
KR101421558B1 (en) | 2007-02-13 | 2014-07-24 | 에스케이텔레콤 주식회사 | Method for Allocating an Address of Device in Wireless Personal Area Network(WPAN) and WPAN Device |
US8123686B2 (en) | 2007-03-01 | 2012-02-28 | Abbott Diabetes Care Inc. | Method and apparatus for providing rolling data in communication systems |
KR101421240B1 (en) | 2007-03-02 | 2014-07-18 | 삼성전자주식회사 | A router and queue process method thereof |
US20090093687A1 (en) | 2007-03-08 | 2009-04-09 | Telfort Valery G | Systems and methods for determining a physiological condition using an acoustic monitor |
US7659823B1 (en) * | 2007-03-20 | 2010-02-09 | At&T Intellectual Property Ii, L.P. | Tracking variable conditions using radio frequency identification |
US20080234943A1 (en) | 2007-03-20 | 2008-09-25 | Pinaki Ray | Computer program for diabetes management |
US9029157B2 (en) | 2007-04-12 | 2015-05-12 | Nipro Diagnostics, Inc. | Error detection and rejection for a diagnostic testing system |
ES2817503T3 (en) | 2007-04-14 | 2021-04-07 | Abbott Diabetes Care Inc | Procedure and apparatus for providing data processing and control in a medical communication system |
EP2146625B1 (en) | 2007-04-14 | 2019-08-14 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
CA2683959C (en) | 2007-04-14 | 2017-08-29 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
CA2683721C (en) | 2007-04-14 | 2017-05-23 | Abbott Diabetes Care Inc. | Method and apparatus for providing dynamic multi-stage signal amplification in a medical device |
CA2683953C (en) | 2007-04-14 | 2016-08-02 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in medical communication system |
WO2008128210A1 (en) | 2007-04-14 | 2008-10-23 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in medical communication system |
CA2685374A1 (en) | 2007-04-27 | 2008-11-06 | Abbott Diabetes Care Inc. | Test strip identification using conductive patterns |
US8692655B2 (en) | 2007-05-07 | 2014-04-08 | Bloomberg Finance L.P. | Dynamically programmable RFID transponder |
US20080281171A1 (en) | 2007-05-08 | 2008-11-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods |
US8461985B2 (en) | 2007-05-08 | 2013-06-11 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8456301B2 (en) | 2007-05-08 | 2013-06-04 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US20080281179A1 (en) | 2007-05-08 | 2008-11-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods |
US7928850B2 (en) | 2007-05-08 | 2011-04-19 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods |
US8239166B2 (en) | 2007-05-14 | 2012-08-07 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
EP2156684A4 (en) | 2007-05-14 | 2012-10-24 | Abbott Diabetes Care Inc | Method and apparatus for providing data processing and control in a medical communication system |
US8260558B2 (en) | 2007-05-14 | 2012-09-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8103471B2 (en) | 2007-05-14 | 2012-01-24 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8600681B2 (en) | 2007-05-14 | 2013-12-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US10002233B2 (en) | 2007-05-14 | 2018-06-19 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20080312845A1 (en) | 2007-05-14 | 2008-12-18 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8444560B2 (en) | 2007-05-14 | 2013-05-21 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US9125548B2 (en) | 2007-05-14 | 2015-09-08 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8560038B2 (en) | 2007-05-14 | 2013-10-15 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US7996158B2 (en) | 2007-05-14 | 2011-08-09 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US20080294024A1 (en) | 2007-05-24 | 2008-11-27 | Cosentino Daniel L | Glucose meter system and monitor |
ES2693097T3 (en) | 2007-05-30 | 2018-12-07 | Ascensia Diabetes Care Holdings Ag | System and method for managing health data |
KR101391151B1 (en) | 2007-06-01 | 2014-05-02 | 삼성전자주식회사 | Method and apparatus for authenticating between clients using session key shared with server |
US8072310B1 (en) | 2007-06-05 | 2011-12-06 | Pulsed Indigo Inc. | System for detecting and measuring parameters of passive transponders |
WO2008154312A1 (en) | 2007-06-08 | 2008-12-18 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US20080312518A1 (en) | 2007-06-14 | 2008-12-18 | Arkal Medical, Inc | On-demand analyte monitor and method of use |
JP5680960B2 (en) | 2007-06-21 | 2015-03-04 | アボット ダイアベティス ケア インコーポレイテッドAbbott Diabetes Care Inc. | Health care device and method |
US8617069B2 (en) | 2007-06-21 | 2013-12-31 | Abbott Diabetes Care Inc. | Health monitor |
US7804197B2 (en) | 2007-06-29 | 2010-09-28 | Seiko Epson Corporation | Power transmission control device, power transmission device, electronic instrument, and non-contact power transmission system |
EP2170430A2 (en) | 2007-06-29 | 2010-04-07 | Roche Diagnostics GmbH | Method and apparatus for determining and delivering a drug bolus |
US7768386B2 (en) | 2007-07-31 | 2010-08-03 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US8834366B2 (en) | 2007-07-31 | 2014-09-16 | Abbott Diabetes Care Inc. | Method and apparatus for providing analyte sensor calibration |
US20090036760A1 (en) | 2007-07-31 | 2009-02-05 | Abbott Diabetes Care, Inc. | Method and apparatus for providing data processing and control in a medical communication system |
EP2182838B1 (en) | 2007-07-31 | 2016-05-04 | Abbott Diabetes Care Inc. | Method and apparatus for providing data processing and control in a medical communication system |
US7731658B2 (en) * | 2007-08-16 | 2010-06-08 | Cardiac Pacemakers, Inc. | Glycemic control monitoring using implantable medical device |
US9968742B2 (en) | 2007-08-29 | 2018-05-15 | Medtronic Minimed, Inc. | Combined sensor and infusion set using separated sites |
US20090063402A1 (en) | 2007-08-31 | 2009-03-05 | Abbott Diabetes Care, Inc. | Method and System for Providing Medication Level Determination |
MX2010003205A (en) | 2007-09-24 | 2010-04-09 | Bayer Healthcare Llc | Multi-electrode test sensors. |
DE102007047351A1 (en) | 2007-10-02 | 2009-04-09 | B. Braun Melsungen Ag | System and method for monitoring and controlling blood glucose levels |
US20090085768A1 (en) | 2007-10-02 | 2009-04-02 | Medtronic Minimed, Inc. | Glucose sensor transceiver |
US9167505B2 (en) | 2007-10-08 | 2015-10-20 | Qualcomm Incorporated | Access management for wireless communication |
US8377031B2 (en) | 2007-10-23 | 2013-02-19 | Abbott Diabetes Care Inc. | Closed loop control system with safety parameters and methods |
US8000918B2 (en) | 2007-10-23 | 2011-08-16 | Edwards Lifesciences Corporation | Monitoring and compensating for temperature-related error in an electrochemical sensor |
US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
US7783442B2 (en) | 2007-10-31 | 2010-08-24 | Medtronic Minimed, Inc. | System and methods for calibrating physiological characteristic sensors |
US8098201B2 (en) * | 2007-11-29 | 2012-01-17 | Electronics & Telecommunications Research Institute | Radio frequency identification tag and radio frequency identification tag antenna |
US8103241B2 (en) * | 2007-12-07 | 2012-01-24 | Roche Diagnostics Operations, Inc. | Method and system for wireless device communication |
MX2010006390A (en) * | 2007-12-10 | 2010-06-25 | Bayer Healthcare Llc | Rapid charging and power management of a battery-powered fluid analyte meter. |
CL2008001569A1 (en) | 2007-12-10 | 2009-01-16 | Bayer Healthcare Llc | Health data monitoring and testing systems comprising a user interface that includes a display and input device, and a self-registration property that provides a user with selectable options for entering health data information; associated methods for providing such systems. |
US8290559B2 (en) | 2007-12-17 | 2012-10-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US20090164190A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Physiological condition simulation device and method |
US20090164239A1 (en) | 2007-12-19 | 2009-06-25 | Abbott Diabetes Care, Inc. | Dynamic Display Of Glucose Information |
JP2011510402A (en) * | 2008-01-15 | 2011-03-31 | コーニング ケーブル システムズ エルエルシー | RFID system and method for automatically detecting and / or indicating the physical configuration of a complex system |
DE102008008072A1 (en) | 2008-01-29 | 2009-07-30 | Balluff Gmbh | sensor |
WO2009097450A1 (en) | 2008-01-30 | 2009-08-06 | Dexcom. Inc. | Continuous cardiac marker sensor system |
JP5091881B2 (en) | 2008-02-20 | 2012-12-05 | カルソニックカンセイ株式会社 | Collision detection device |
US20090299156A1 (en) | 2008-02-20 | 2009-12-03 | Dexcom, Inc. | Continuous medicament sensor system for in vivo use |
WO2009105709A1 (en) | 2008-02-21 | 2009-08-27 | Dexcom, Inc. | Systems and methods for processing, transmitting and displaying sensor data |
CN101965151B (en) | 2008-03-10 | 2012-12-05 | 皇家飞利浦电子股份有限公司 | Wireless ECG monitoring system |
US8396528B2 (en) | 2008-03-25 | 2013-03-12 | Dexcom, Inc. | Analyte sensor |
US20090242399A1 (en) | 2008-03-25 | 2009-10-01 | Dexcom, Inc. | Analyte sensor |
CN102047101A (en) | 2008-03-28 | 2011-05-04 | 德克斯康公司 | Polymer membranes for continuous analyte sensors |
WO2009125421A1 (en) | 2008-04-11 | 2009-10-15 | Indian Institute Of Science | A sub-threshold capfet sensor for sensing analyte, a method and system thereof |
US20090267765A1 (en) | 2008-04-29 | 2009-10-29 | Jack Greene | Rfid to prevent reprocessing |
US8102021B2 (en) * | 2008-05-12 | 2012-01-24 | Sychip Inc. | RF devices |
WO2009140360A1 (en) | 2008-05-14 | 2009-11-19 | Espenuda Holding, Llc | Physical activity monitor and data collection unit |
WO2009143289A2 (en) | 2008-05-20 | 2009-11-26 | Deka Products Limited Partnership | Rfid system |
US9356473B2 (en) | 2008-05-28 | 2016-05-31 | Georgia Tech Research Corporation | Systems and methods for providing wireless power to a portable unit |
US7826382B2 (en) | 2008-05-30 | 2010-11-02 | Abbott Diabetes Care Inc. | Close proximity communication device and methods |
US8394637B2 (en) * | 2008-06-02 | 2013-03-12 | Roche Diagnostics Operations, Inc. | Handheld analyzer for testing a sample |
US8132037B2 (en) * | 2008-06-06 | 2012-03-06 | Roche Diagnostics International Ag | Apparatus and method for processing wirelessly communicated data and clock information within an electronic device |
US8117481B2 (en) * | 2008-06-06 | 2012-02-14 | Roche Diagnostics International Ag | Apparatus and method for processing wirelessly communicated information within an electronic device |
WO2010005806A2 (en) * | 2008-07-09 | 2010-01-14 | Cardiac Pacemakers, Inc. | Event-based battery monitor for implantable devices |
WO2010009172A1 (en) | 2008-07-14 | 2010-01-21 | Abbott Diabetes Care Inc. | Closed loop control system interface and methods |
US20100025238A1 (en) * | 2008-07-31 | 2010-02-04 | Medtronic Minimed, Inc. | Analyte sensor apparatuses having improved electrode configurations and methods for making and using them |
US8111042B2 (en) * | 2008-08-05 | 2012-02-07 | Broadcom Corporation | Integrated wireless resonant power charging and communication channel |
US8432070B2 (en) | 2008-08-25 | 2013-04-30 | Qualcomm Incorporated | Passive receivers for wireless power transmission |
US8094009B2 (en) * | 2008-08-27 | 2012-01-10 | The Invention Science Fund I, Llc | Health-related signaling via wearable items |
US20100057040A1 (en) | 2008-08-31 | 2010-03-04 | Abbott Diabetes Care, Inc. | Robust Closed Loop Control And Methods |
US8734422B2 (en) | 2008-08-31 | 2014-05-27 | Abbott Diabetes Care Inc. | Closed loop control with improved alarm functions |
US9943644B2 (en) | 2008-08-31 | 2018-04-17 | Abbott Diabetes Care Inc. | Closed loop control with reference measurement and methods thereof |
US8102154B2 (en) * | 2008-09-04 | 2012-01-24 | Medtronic Minimed, Inc. | Energy source isolation and protection circuit for an electronic device |
WO2010031059A2 (en) | 2008-09-15 | 2010-03-18 | Deka Products Limited Partnership | Systems and methods for fluid delivery |
US20100095229A1 (en) | 2008-09-18 | 2010-04-15 | Abbott Diabetes Care, Inc. | Graphical user interface for glucose monitoring system |
EP2326944B1 (en) | 2008-09-19 | 2020-08-19 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
JP2012504932A (en) | 2008-10-02 | 2012-02-23 | レイデン エナジー インコーポレイテッド | Electronic current interrupt device for batteries |
WO2010040090A2 (en) * | 2008-10-03 | 2010-04-08 | Bayer Healthcare Llc | System and method for predicting ambient temperature in a fluid analyte meter |
US8098161B2 (en) * | 2008-12-01 | 2012-01-17 | Raytheon Company | Radio frequency identification inlay with improved readability |
US8150516B2 (en) | 2008-12-11 | 2012-04-03 | Pacesetter, Inc. | Systems and methods for operating an implantable device for medical procedures |
US20100169035A1 (en) | 2008-12-29 | 2010-07-01 | Medtronic Minimed, Inc. | Methods and systems for observing sensor parameters |
US9320470B2 (en) | 2008-12-31 | 2016-04-26 | Medtronic Minimed, Inc. | Method and/or system for sensor artifact filtering |
US8974439B2 (en) | 2009-01-02 | 2015-03-10 | Asante Solutions, Inc. | Infusion pump system and methods |
US9402544B2 (en) | 2009-02-03 | 2016-08-02 | Abbott Diabetes Care Inc. | Analyte sensor and apparatus for insertion of the sensor |
EP2394217A4 (en) | 2009-02-04 | 2016-05-04 | Abbott Diabetes Care Inc | Multi-function analyte test device and methods therefor |
US8394246B2 (en) | 2009-02-23 | 2013-03-12 | Roche Diagnostics Operations, Inc. | System and method for the electrochemical measurement of an analyte employing a remote sensor |
US9226701B2 (en) | 2009-04-28 | 2016-01-05 | Abbott Diabetes Care Inc. | Error detection in critical repeating data in a wireless sensor system |
EP2424426B1 (en) | 2009-04-29 | 2020-01-08 | Abbott Diabetes Care, Inc. | Method and system for providing data communication in continuous glucose monitoring and management system |
US8595607B2 (en) | 2009-06-04 | 2013-11-26 | Abbott Diabetes Care Inc. | Method and system for updating a medical device |
US8124452B2 (en) * | 2009-06-14 | 2012-02-28 | Terepac Corporation | Processes and structures for IC fabrication |
JP5326044B2 (en) | 2009-06-17 | 2013-10-30 | ヴェーデクス・アクティーセルスカプ | Method for initializing binaural hearing aid system and hearing aid |
CA2957078C (en) | 2009-06-30 | 2019-04-30 | Lifescan, Inc | Analyte testing methods and device for calculating basal insulin therapy |
US9792408B2 (en) * | 2009-07-02 | 2017-10-17 | Covidien Lp | Method and apparatus to detect transponder tagged objects and to communicate with medical telemetry devices, for example during medical procedures |
AU2010284320B2 (en) | 2009-08-17 | 2015-02-26 | The Regents Of The University Of California | Distributed external and internal wireless sensor systems for characterization of surface and subsurface biomedical structure and condition |
WO2011026148A1 (en) | 2009-08-31 | 2011-03-03 | Abbott Diabetes Care Inc. | Analyte monitoring system and methods for managing power and noise |
EP3923295A1 (en) | 2009-08-31 | 2021-12-15 | Abbott Diabetes Care, Inc. | Medical devices and methods |
US9314195B2 (en) | 2009-08-31 | 2016-04-19 | Abbott Diabetes Care Inc. | Analyte signal processing device and methods |
ES2912584T3 (en) | 2009-08-31 | 2022-05-26 | Abbott Diabetes Care Inc | A glucose monitoring system and method |
US8093991B2 (en) * | 2009-09-16 | 2012-01-10 | Greatbatch Ltd. | RFID detection and identification system for implantable medical devices |
US20110270112A1 (en) | 2009-11-02 | 2011-11-03 | Applied Cardiac Systems, Inc. | Multi-Function Health Monitor |
US8478389B1 (en) | 2010-04-23 | 2013-07-02 | VivaQuant, LLC | System for processing physiological data |
CN102687418B (en) | 2009-11-13 | 2016-08-17 | 皇家飞利浦电子股份有限公司 | System and method and communication unit for the physiological data that communicates |
KR101414103B1 (en) | 2009-12-08 | 2014-07-02 | 엘지디스플레이 주식회사 | Transparent liquid crystal display device |
US9949672B2 (en) | 2009-12-17 | 2018-04-24 | Ascensia Diabetes Care Holdings Ag | Apparatus, systems and methods for determining and displaying pre-event and post-event analyte concentration levels |
US20110184268A1 (en) | 2010-01-22 | 2011-07-28 | Abbott Diabetes Care Inc. | Method, Device and System for Providing Analyte Sensor Calibration |
WO2011133768A1 (en) | 2010-04-22 | 2011-10-27 | Abbott Diabetes Care Inc. | Devices, systems, and methods related to analyte monitoring and management |
US10092229B2 (en) | 2010-06-29 | 2018-10-09 | Abbott Diabetes Care Inc. | Calibration of analyte measurement system |
US8849459B2 (en) * | 2010-10-15 | 2014-09-30 | Roche Diagnostics Operations, Inc. | Power management system for a handheld medical device |
US20130035865A1 (en) | 2011-08-05 | 2013-02-07 | Dexcom, Inc. | Systems and methods for detecting glucose level data patterns |
US20130235166A1 (en) | 2012-03-07 | 2013-09-12 | Cambridge Silicon Radio Limited | Synchronisation method |
-
2010
- 2010-08-31 WO PCT/US2010/047413 patent/WO2011026148A1/en active Application Filing
- 2010-08-31 US US12/873,298 patent/US8993331B2/en active Active
- 2010-08-31 EP EP10812782.0A patent/EP2473099A4/en not_active Withdrawn
-
2015
- 2015-03-26 US US14/669,842 patent/US10429250B2/en active Active
-
2019
- 2019-10-01 US US16/589,819 patent/US11150145B2/en active Active
-
2021
- 2021-10-19 US US17/504,986 patent/US11635332B2/en active Active
-
2023
- 2023-03-10 US US18/182,031 patent/US20230273071A1/en active Pending
Patent Citations (6)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5659454A (en) * | 1993-12-01 | 1997-08-19 | Neopost Industrie | Thermal protection apparatus for a secure electronic appliance, in particular a postage meter |
US5581206A (en) * | 1995-07-28 | 1996-12-03 | Micron Quantum Devices, Inc. | Power level detection circuit |
US6937222B2 (en) * | 2001-01-18 | 2005-08-30 | Sharp Kabushiki Kaisha | Display, portable device, and substrate |
US7228162B2 (en) * | 2003-01-13 | 2007-06-05 | Isense Corporation | Analyte sensor |
US7408132B2 (en) * | 2004-11-08 | 2008-08-05 | Rrc Power Solutions Gmbh | Temperature sensor for power supply |
US20080278332A1 (en) * | 2007-05-08 | 2008-11-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and methods |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US11690538B2 (en) | 2013-12-16 | 2023-07-04 | Dexcom, Inc. | Systems and methods for monitoring and managing life of a battery in an analyte sensor system worn by a user |
CN108025278A (en) * | 2015-02-24 | 2018-05-11 | 实验风格创意有限公司 | System and method for adjusting the power level in monitoring device |
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US20220283042A1 (en) | 2022-09-08 |
US20200103291A1 (en) | 2020-04-02 |
US11635332B2 (en) | 2023-04-25 |
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US8993331B2 (en) | 2015-03-31 |
EP2473099A4 (en) | 2015-01-14 |
US11150145B2 (en) | 2021-10-19 |
US20110054282A1 (en) | 2011-03-03 |
US20230273071A1 (en) | 2023-08-31 |
EP2473099A1 (en) | 2012-07-11 |
US20150198488A1 (en) | 2015-07-16 |
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