US20060213519A1 - Control of respiratory oxygen delivery - Google Patents
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- US20060213519A1 US20060213519A1 US11/441,525 US44152506A US2006213519A1 US 20060213519 A1 US20060213519 A1 US 20060213519A1 US 44152506 A US44152506 A US 44152506A US 2006213519 A1 US2006213519 A1 US 2006213519A1
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/10—Preparation of respiratory gases or vapours
- A61M16/1005—Preparation of respiratory gases or vapours with O2 features or with parameter measurement
- A61M16/101—Preparation of respiratory gases or vapours with O2 features or with parameter measurement using an oxygen concentrator
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- A—HUMAN NECESSITIES
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0051—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes with alarm devices
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/021—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes operated by electrical means
- A61M16/022—Control means therefor
- A61M16/024—Control means therefor including calculation means, e.g. using a processor
- A61M16/026—Control means therefor including calculation means, e.g. using a processor specially adapted for predicting, e.g. for determining an information representative of a flow limitation during a ventilation cycle by using a root square technique or a regression analysis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/06—Respiratory or anaesthetic masks
- A61M16/0666—Nasal cannulas or tubing
- A61M16/0672—Nasal cannula assemblies for oxygen therapy
- A61M16/0677—Gas-saving devices therefor
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
- A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
- A61M2016/0021—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with a proportional output signal, e.g. from a thermistor
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/0015—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors
- A61M2016/0018—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical
- A61M2016/0024—Accessories therefor, e.g. sensors, vibrators, negative pressure inhalation detectors electrical with an on-off output signal, e.g. from a switch
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
- A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
- A61M2016/0027—Accessories therefor, e.g. sensors, vibrators, negative pressure pressure meter
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M2202/00—Special media to be introduced, removed or treated
- A61M2202/02—Gases
- A61M2202/0208—Oxygen
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2202/00—Special media to be introduced, removed or treated
- A61M2202/03—Gases in liquid phase, e.g. cryogenic liquids
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- A—HUMAN NECESSITIES
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- A61M2205/00—General characteristics of the apparatus
- A61M2205/35—Communication
- A61M2205/3546—Range
- A61M2205/3561—Range local, e.g. within room or hospital
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/20—Blood composition characteristics
- A61M2230/205—Blood composition characteristics partial oxygen pressure (P-O2)
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M2230/00—Measuring parameters of the user
- A61M2230/63—Motion, e.g. physical activity
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Abstract
Methods and systems for supplying respiratory oxygen to users when the users are inhaling are disclosed. The methods and systems may rely on delivery devices that are selectively placed in fluid communication with either a respiration sensor or a source of oxygen. The methods and systems may actively monitor for exhalations, as well as monitor for oxygen in the oxygen source. The respiration sensor may preferably be a flow sensor.
Description
- This is a continuation of U.S. patent application Ser. No. 10/695,436, filed 28 Oct. 2003, which is a continuation of U.S. patent application Ser. No. 10/370,799, filed 20 Feb. 2003, which is a continuation of U.S. patent application Ser. No. 10/076,001, filed 14 Feb. 2002, (issued as U.S. Pat. No. 6,561,187), which is a continuation of U.S. patent application Ser. No. 09/463,614, filed 25 Jan. 2000 (with a 35 U.S.C. §371 date of May 8, 2000, now issued as U.S. Pat. No. 6,371,114), which is a U.S. National Stage Application of PCT/US98/15490, filed 24 Jul. 1998, which claims priority to U.S. Provisional Patent Application Ser. No. 60/064,578, filed 4 Nov. 1997 and which also claims priority to (and is a continuation-in-part of) U.S. patent application Ser. No. 08/900,686 filed 25 Jul. 1997, (issued as U.S. Pat. No. 6,532,958). All of the above-identified patent applications are incorporated herein by reference in their respective entireties
- The present invention relates to the field of respiratory oxygen supply systems and methods. More particularly, the present invention provides demand delivery methods and systems that supply respiratory oxygen when the patient is inhaling.
- Respiratory oxygen is delivered to patients in both sub-critical care situations in which oxygen is provided as a supplement to room air that may be inhaled by the patients (often referred to as “supplemental” oxygen delivery) and in critical care situations in which the gases (particularly oxygen) inspired by patients are closely controlled, possibly in connection with blood gas measurements.
- Continuous oxygen delivery in sub-critical and critical care is, however, wasteful because oxygen is only needed by patients when they are inhaling and the oxygen delivered at other times is wasted. In supplemental oxygen delivery, the most significant financial cost associated with this waste is found in the increased service visits required by the oxygen provider to replenish the patient's oxygen supply, because the actual cost of the oxygen is only a small fraction of the total cost of the therapy. In critical care environments, the capacity of the oxygen delivery system must be increased to account for the oxygen delivered when the patient is exhaling.
- One approach to conserving the oxygen delivered to patients is typically referred to as “demand delivery.” The demand delivery systems respond to a patient's inspiratory effort by attempting to deliver oxygen during the period of inhalation, rather than allow the oxygen to flow to the patient continuously. There are many ways in which this basic concept has been implemented.
- A variety of respiration detection systems have been developed in connection with demand delivery systems. Examples of some respiration detectors include a chest belt worn by the patient that generates an electrical signal to trigger the opening of the oxygen supply valve; a hand-activated breathing device attached to a portable gas bottle via a supply hose in which users dispense the oxygen by pushing a button while holding the device next to their mouth; a mechanical chest strap/valve that functions as both an inhalation sensor and delivery device in an oxygen conserving system; and an all-pneumatic, fluidically-controlled device.
- Other demand delivery systems use pressure sensors in the oxygen line to monitor line pressure at the nostrils. A small negative pressure, indicative of the onset of inhalation, is often relied on to trigger the release of oxygen. This type of detection scheme has become a standard method of demand delivery and is employed by most systems currently in use.
- Yet another approach employs flow sensors to monitor patient respiration. In many of these demand delivery systems, the flow sensors are located in-line with the source of oxygen such that, in addition to monitoring patient respiration, the flow sensors also monitor the amount of oxygen passing through them during the oxygen delivery portion of the cycle. It is, however, difficult (if not impossible) to accomplish both of those functions with a single flow sensor because the flow rates that need to be sensed differ by orders of magnitude. For example, when measured using a nasal cannula, patient respiration may result in flow rates at the flow sensor of about 1 cubic centimeters per minute (cc/min) or less, while the flow rate of oxygen delivered to the patient can be up to about 15 liters per minute (1/min) or more. One significant problem is in sensing inhalation or exhalation simultaneously with the delivery of oxygen in these situations. Examples of this approach are found in U.S. Pat. No. 4,823,788 (Smith et al.) and U.S. Pat. No. 5,558,086 (Smith et al.).
- In addition to the above-listed problems, even if the flow sensor has a dynamic range capable of sensing respiration and delivery oxygen, the systems do not allow for correction in the “drift” often associated with such sensors. In other words, over time the accuracy of the sensor may be impaired because of dynamic changes in the flow sensor during use. Because the flow sensors are always in use, monitoring either oxygen flow or respiration, adjustments are difficult if not impossible to make to correct for voltage drift.
- Another flow sensor-based demand delivery system is described in U.S. Pat. No. 5,074,299 (Dietz) in which a flow sensor is connected to one port of a nasal cannula while oxygen is delivered through the other port of the cannula. One disadvantage to this approach is that if one side of the patient's nasal cavity is blocked due to an upper respiratory infection or cold, the system will either be unable to effectively deliver oxygen or sense respiration (depending on which port of the cannula is located on the blocked side).
- Even if the patient is not experiencing blockage, it may be difficult for the sensor to detect exhalation if the patient is breathing through his or her mouth. The nasal respiratory flow rate is significantly reduced in such patients, and if flow sensing is occurring only through one port in the cannula, it may be too low to be accurately detected. Another disadvantage is that the system requires a more expensive and obscure dual-line cannula.
- Regardless of whether pressure or flow sensors are used to detect respiration, shallow respiration can make respiration sensing in systems relying on pressure/flow sensors difficult or impossible because the flow volume and/or flow rate of gases associated with respiration deteriorate as the gases from inhalation or exhalation travel through the lines connecting the patient's respiratory system to the sensor. The flow volume/rate deterioration caused by the lines further reduces the flow volume/rate produced by a patient engaging in shallow respiration. As a result, the respiration sensor may be unable to detect respiration or may detect only a portion of the actual inhalation/exhalation events.
- Another problem associated with patients experiencing rapid respiration rates is that some demand delivery systems include a time delay period to prevent sensing of the same inhalation period more than once. These systems operate on the assumption that each inhalation lasts for a predetermined minimum amount of time and the system is prevented from sensing inhalation within the delay period. Because the patient is, however, experiencing rapid respiration, the patient may actually inhale two or more times during the delay period. The effect of such a “lockout” feature is that the patient will receive oxygen during only a fraction of their inhalation events. In addition, if the respirations are rapid and the system delivers oxygen too slowly, the patient may already be exhaling by the time the system begins to deliver oxygen.
- The present invention provides respiratory oxygen supply methods and systems. In some aspects, the systems/methods rely on respiration sensors sensing variations in patient respiration to determine when a patient is inhaling and allow for the determination of an inhalation event after exhalation has been determined. In other aspects, the respiration sensors may be advantageously used to detect the presence of oxygen from the oxygen supply. In still other aspects, when the present invention uses a flow sensor as a respiration sensor, the system may automatically correct for variations in the signals provided by the flow sensor using a zero-flow offset signal, thereby improving the accuracy of the system.
- In one aspect, the present invention provides a method of delivering respiratory oxygen to a patient by providing an oxygen delivery system including an oxygen delivery device, a respiration sensor, and an oxygen source; placing the delivery device in fluid communication with the respiration sensor and monitoring variations in respiration with the respiration sensor to determine when the patient is inhaling; placing the oxygen source in fluid communication with the delivery device; delivering oxygen to the delivery device from the oxygen source when the patient is inhaling; removing the respiration sensor from fluid communication with the delivery device when delivering oxygen to the delivery device from the oxygen source; placing the respiration sensor in fluid communication with the delivery device after delivering oxygen to the delivery device from the oxygen source; monitoring variations in respiration with the respiration sensor after delivering oxygen to the delivery device from the oxygen source to determine when the patient is exhaling; and resuming the monitoring of variations in respiration with the respiration sensor to determine that the patient is inhaling after determining that the patient has exhaled.
- In another aspect, the present invention provides a method of delivering respiratory oxygen to a patient by providing an oxygen delivery system including an oxygen delivery device, a respiration sensor, and an oxygen source; placing the delivery device in fluid communication with the respiration sensor and monitoring variations in respiration with the respiration sensor to determine when the patient is inhaling; placing the oxygen source in fluid communication with the delivery device; delivering oxygen to the delivery device from the oxygen source when the patient is inhaling; removing the respiration sensor from fluid communication with the delivery device when delivering oxygen to the delivery device from the oxygen source; placing the respiration sensor in fluid communication with the delivery device after delivering oxygen to the delivery device from the oxygen source; and monitoring the respiration sensor to detect oxygen in the oxygen source.
- In another aspect, the present invention provides a method of delivering respiratory oxygen to a patient by providing an oxygen delivery system including an oxygen delivery device, a flow sensor, and an oxygen source; placing the delivery device in fluid communication with the flow sensor and monitoring variations in respiration with the flow sensor to determine when the patient is inhaling; placing the oxygen source in fluid communication with the delivery device; delivering oxygen to the delivery device from the oxygen source when the patient is inhaling; removing the respiration sensor from fluid communication with the delivery device when delivering oxygen to the delivery device from the oxygen source; placing the flow sensor in fluid communication with the delivery device after delivering oxygen to the delivery device from the oxygen source; monitoring a zero-flow offset signal produced by the flow sensor when it is not in fluid communication with the delivery device; and compensating for drift in the zero-flow offset signal generated by the flow sensor based on the monitoring when the flow sensor is not in fluid communication with the delivery device.
- In another aspect, the present invention provides a method of delivering respiratory oxygen to a patient by providing an oxygen delivery system including an oxygen delivery device, a bidirectional flow sensor vented to atmosphere, and an oxygen source; placing the delivery device in fluid communication with the flow sensor and monitoring variations in respiration with the flow sensor to determine when the patient is inhaling; placing the oxygen source in fluid communication with the delivery device; delivering oxygen to the delivery device from the oxygen source when the patient is inhaling; removing the flow sensor from fluid communication with the delivery device when delivering oxygen to the delivery device from the oxygen source; placing the flow sensor in fluid communication with the delivery device after delivering oxygen to the delivery device from the oxygen source; monitoring variations in respiration with the flow sensor when it is in fluid communication with the delivery device to determine when the patient is exhaling before resuming the monitoring of variations in respiration with the flow sensor to determine that the patient is inhaling; monitoring a zero-flow offset signal produced by the flow sensor when it is not in fluid communication with the delivery device; compensating for drift in the zero-flow offset signal generated by the flow sensor based on the monitoring when the flow sensor is not in fluid communication with the delivery device; and monitoring the flow sensor to detect oxygen in the oxygen source when switching the delivery device from fluid communication with either of the oxygen source and the flow sensor.
- In another aspect, the present invention provides a system for delivering respiratory oxygen to a patient including a delivery line adapted for connection to an oxygen delivery device located on a patient; a source line adapted for connection to an oxygen source; a respiration sensor; at least one valve in fluid communication with the delivery line, the source line and the respiration sensor; wherein the at least one valve places the delivery line in fluid communication with only one of the source line and the respiration sensor at any given time; means for monitoring the respiration sensor for variations in respiration of a patient; means for determining when the patient is inhaling and exhaling based on the monitoring of the respiration sensor; and means for preventing a determination that the patient is inhaling until after a determination that the patient has exhaled has been made.
- In another aspect, the present invention provides a system for delivering respiratory oxygen to a patient including a delivery line adapted for connection to an oxygen delivery device located on a patient; a source line adapted for connection to an oxygen source; a respiration sensor; at least one valve in fluid communication with the delivery line, the source line and the respiration sensor; wherein the at least one valve places the delivery line in fluid communication with only one of the source line and the respiration sensor at any given time; means for monitoring the respiration sensor to detect oxygen in the source line.
- As used in connection with the present invention, the terms “supplemental oxygen” and “supplemental respiratory oxygen” refer to oxygen delivered to patients in addition to the oxygen received by the patient through the inspiration of room or ambient air. Because room air contains some oxygen, the supplemental oxygen is provided in addition to the oxygen that would normally be inspired by the patient.
- As used in connection with the present invention, the term “blood oxygen content” and “blood oxygen content level” will typically be used to refer to blood oxygen saturation as commonly measured by the percentage of oxygen-saturated hemoglobin (SpO2) although it can also refer to any suitable measurement for determining the level of oxygenation in a patient's blood. For example, it will be understood that blood oxygen content can also be obtained based on data from a CO-oximeter. Furthermore, blood oxygen content, can also be obtained based on partial pressures of oxygen (PaO2).
- As used in connection with the present invention, the term “sub-acute care” refers to care provided to patients that is not intended to treat critical conditions. Typically, sub-acute care is provided to patients in residential settings. “Residential” preferably includes, e.g., homes and long-term care facilities (such as nursing homes). Sub-acute care also includes care delivered in ambulatory situations, i.e., when the patient is engaged in normal activities outside of his or her residence, such as shopping, attending concerts or other events, traveling to appointments with health care professionals, etc.
- As used in connection with the present invention, the terms “continuous” and “continuously” (when referring to the measuring of blood oxygen content levels) mean that the blood oxygen content level of the patient will be measured without cessation or at intervals (fixed or variable) that are sufficiently small to provide the advantages of the invention.
- These and other features and advantages of the present invention will be apparent upon review of the detailed description of the invention and accompanying drawings.
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FIG. 1 is a block diagram of one system according to the present invention. -
FIG. 2 is a block diagram of one demand delivery module for use in a system such as that depicted inFIG. 1 . -
FIG. 3 a is a flow diagram of one method according to the present invention. -
FIG. 3 b is a flow diagram of another method according to the present invention. -
FIG. 4 is a flow diagram of one method of delivering supplemental oxygen based on whether the measured blood oxygen content data is valid or invalid. - As described above, the present invention provides demand respirating oxygen supply methods and apparatus for use in sub-acute care which maintain healthy blood oxygen saturation in patients by controlled dosing of oxygen with a measured response to the patient's actual blood oxygen content. The dosing can be provided by simple on/off control over the delivery of oxygen or the amount of oxygen delivered to the patient with each inhalation can be varied in response to the patient's need as determined by a more sophisticated control scheme, such as a proportional-integral-derivative (PID) loop control algorithm, that utilizes the difference between the patient's measured blood oxygen content level and a desired or target blood oxygen content level.
- The systems and methods of the present invention are particularly directed at patients receiving supplemental oxygen in a sub-acute care environment, more preferably in a residential setting. The needs and considerations of patients receiving supplemental oxygen in sub-acute care differ from those present when providing oxygen to patients in critical care environments, in which the amounts of oxygen delivered to patients are carefully controlled in connection with masks or other enclosures that do not typically allow the patents to inspire room air in uncontrolled manners. In those situations, the fractional amount of inspired oxygen (FIO2) is typically controlled by mixing oxygen and air in a blender or other device before delivering the gas to the patient.
- Among the advantages of the present invention are the significant conservation of oxygen provided by delivering only the amount of oxygen needed to maintain a healthy blood oxygen content and the ability to address therapeutic problems associated with demand delivery systems by providing the correct amount of oxygen to the patient to reduce uncontrolled hypoxic events.
- The amounts of oxygen that can be conserved by implementing the methods according to the present invention can be significant, even compared to known demand delivery systems that conserve oxygen by simply turning the supply on or off during a patient's respiration. Studies have reported oxygen savings ratios of from 3:1 to 7:1 for known simple demand delivery systems. In other words, a fixed amount of oxygen can last three to seven times as long as the same amount of oxygen would last in a supplemental oxygen delivery system that does not include a simple demand delivery system. Implementation of the methods according to the present invention by using a demand delivery approach with a feedback control mechanism that responds to a continuous blood oxygenation measurement could provide an oxygen savings ratio of greater than 13:1 while maintaining the patient's SaO2 at the 90% level.
- Other advantages of the methods and apparatus according to the present invention are the ability to integrate the invention with any sub-acute care supplemental oxygen supply system, including both ambulatory and stationary sources. For unlimited volume sources, such as oxygen concentrators and membrane separators, the invention will reduce their size and energy consumption for a given level of therapy. For fixed volume gas sources, such as liquid and high pressure gas, the invention will extend the lifetime of the oxygen supply, thereby significantly decreasing the cost of providing that treatment.
- If the system is ambulatory, the present invention can allow for reductions in the size and weight of the oxygen source, thereby increasing the patient's mobility. An added benefit of reducing the size and/or weight of the ambulatory systems is the potential for a better therapeutic outcome. If patients find the smaller, lighter weight systems less cosmetically unattractive they will be more likely to carry and use the systems during ambulatory activities as opposed to not using the systems. Studies have shown that the benefit of supplemental oxygen systems is significantly reduced if the systems are not used on a regular basis.
- Another advantage of the invention, method and apparatus, is a reduction in the risk of hypercapnia (carbon dioxide retention) by only providing enough oxygen to reach a predetermined blood oxygen saturation, typically about 90% as measured by a conventional two-color pulse oximeter.
- One embodiment of an automated respiratory oxygen supply system is depicted in
FIG. 1 and includes acontroller 10, ademand delivery module 12, and a bloodoxygen content sensor 14 connected to thepatient 16. Oxygen is supplied from anoxygen source 20 to thepatient 16 by thedemand delivery module 12 through, in the preferred embodiments, a supplementaloxygen delivery device 18. The preferred system may also include auser interface 32 and analarm 38. - The supplemental
oxygen delivery device 18 is preferably a nasal cannula as depicted inFIG. 1 , although it will be understood that the supplemental oxygen delivery device can take the form of any device designed to provide supplemental respiratory oxygen to a patient while not preventing the patient from also inspiring room or ambient air in addition to the supplemental respiratory oxygen from an oxygen source. Examples of other supplemental oxygen delivery devices include, but are not limited to: tracheal catheters, nasal masks designed for use with Continuous Positive Airway Pressure (CPAP) systems, vented masks that cover both the nose and the mouth but that allow inspiration of room air in uncontrolled amounts in addition to the supplemental oxygen delivered to the mask, etc. -
Oxygen source 20 could be an oxygen concentrator, membrane separator, high pressure cylinder or liquid oxygen dewar. This could also include any portable versions ofoxygen sources 20. Other potential sources of oxygen gas suitable for providing supplemental oxygen in sub-acute care in a residential setting and/ambulatory situations may be created in the future and should be considered as being functional with the described invention. As used below, “line” will refer to any connection made between the oxygen source, the described invention and the patient. - If the
oxygen source 20 is an oxygen concentrator, typically a continuous low-flow device, usually delivering at most 6 liters/min of 96% oxygen, the system may also include an oxygen storage device to accommodate the periodic higher flows that are necessary to practice the methods described below. If high flow concentrators become available, such a storage device would not be needed. - One
controller 10 is an electronic circuit including a software programmable microcontroller as its main component. Depending on the allocation of tasks within the device a number of microcontrollers could be used as acontroller 10. In one embodiment, thecontroller 10 includes a serial data input port, A/D converter, LED driver capabilities and digital I/O pins. One example of a suitable controller is the PIC 16C74A microcontroller from Microchip Technology Inc. of Chandler, Ariz. - Those skilled in the art will realize that a great deal of optimization may be done relative to the choice of a microcontroller(s). Specifications, such as power consumption, cost, memory size, clock speed and part availability may alter the choice for a preferred microcontroller. Furthermore, many of the functions described for the microcontroller in the preferred embodiment could be accomplished by using discrete circuits of many types. Additionally, the microcontroller and its peripheral circuitry may be replaced entirely by discrete circuitry, such as programmable logic arrays, A/D converter chips, analog comparators, etc.
- The system also includes an
oxygen content sensor 14 for monitoring the blood oxygen content of thepatient 16. Onesuitable sensor 14 includes asensor control module 14 a and asensor 14 b typically mounted or attached to thepatient 16 by some suitable technique. The information from theoxygen content sensor 14 is fed back to thecontroller 10 for use in executing the methods according to the present invention. It is preferred, but not required, that theoxygen sensor 14 provide a signal to thesystem controller 10 in the form of a blood oxygen saturation in percent. Thesensor 14 preferably, but not necessarily, processes all of its data internally and thecontroller 10 preferably processes only error flags and numerical information as described shortly. - One
preferred oxygen sensor 14 is a non-invasive sensor such as a two-color pulse oximeter. As used herein, the terms “pulse oximeter” or “oxygen sensor” will include both the optical sensor and the circuitry used to determine blood oxygen saturation levels using the optical sensor. One example of a suitable pulse oximeter is a conventional two-color, OEM-II oximeter module, from Nonin Medical Inc. of Plymouth, Minn., that can measure the percentage of oxygen-saturated hemoglobin, SpO2, in the blood stream of an in vivo respiratory system. The preferred embodiment of thepulse oximeter 14 uses a transmitting sensor that attaches to the user's finger. Alternative embodiments may employ sensors that attach elsewhere on the body. - While the pulse oximeter is one preferred non-invasive oxygen sensor, it should be understood that any blood oxygen sensor, invasive or non-invasive, useful for determining blood oxygen content levels (preferably continuously) could be used in connection with the present invention. It should also be apparent to those skilled in the art that technologies on the horizon, such as an implantable, microelectromechanical (MEMS) blood gas analyzer, may provide the blood oxygen content information needed by the
system controller 10. Furthermore, there may be improvements in pulse oximetry technology, such as the ability to determine the level of carboxyhemoglobin in the blood, that may be useful for the described invention. Use of these new blood oxygen content technologies in oxygen conservers for long-term oxygen therapy should be considered to lie within the scope of the systems and methods of the present invention provided they have the ability to provide suitable blood oxygen content measurements. - In one embodiment, the
pulse oximeter 14 deconvolves the optical information into a blood oxygen saturation value, SpO2, in percent. Theoximeter 14 outputs a serial data stream with this information to thecontroller 10 for evaluation. Other important information may also be included in the oximeter data stream, such as the user's pulse rate and error flags that detail the reliability of the SpO2 and pulse rate values. - It will be recognized by those skilled in the art that an alternative embodiment may be provided in which the
system controller 10 functions as thesensor control module 14 a. As a result, data evaluation and error handling would be accomplished within thesystem controller 10 with anappropriate oxygen sensor 14 b being attached to thepatient 16. - Blood oxygen content measuring in connection with the present invention is described as “continuous” although it will be understood that the measurements made using, e.g., pulse oximeters and other devices, may actually be taken at discrete intervals. As discussed above, “continuous” as used in connection with the measuring of blood oxygen content in the present invention includes measurement of the blood oxygen content levels of the patient at intervals (fixed or variable) that are sufficiently small to provide the advantages of the invention. Preferably the sampling intervals will be less than about five minutes, more preferably less than about one minute, and even more preferably less than about one respiration interval (i.e., the time between the onset of two inhalations by the patient).
- The information relating to blood oxygen content provided by the
oxygen sensor 16 is then used by thesystem controller 10 in combination with thedemand delivery module 12 to provide control over the oxygen supplied to the patient 16 from theoxygen source 20 as described in connection with the methods according to the present invention below. - A block diagram illustrating the components of one embodiment of a
demand delivery module 12 according to the present invention is depicted inFIG. 2 . One component in thedemand delivery module 12 is an inhalation orrespiration sensor 40 that monitors the respiratory activity of the patient 16 to determine variations in respiration of the patient. It is preferred that the variations in respiration allow the determination of when the patient is inhaling, although other portions of the respiratory cycle may actually be sensed. In other words, inhalation is preferably sensed, but in some cases it may be desirable to determine when inhalation is occurring based on the sensing of some other condition, activity, etc. such as chest movement, exhalation, etc. - In one embodiment, the
respiration sensor 40 provides a signal to a respiration sensor/valve controller 42 that, in turn, controls thevalve 26 based on additional input from system controller 10 (as will be described in more detail below). - The
respiration sensor 40 can take a variety of forms that will be known to those skilled in the art. One type ofsuitable respiration sensor 40 monitors flow in the line used to supply oxygen to the supplementaloxygen delivery device 18. Thesensor 40 inFIG. 2 monitors flow through thevalve 26 interposed in the line between the supplementaloxygen delivery device 18 and theoxygen source 20. One suitable flow sensor is a Honeywell AWM2150 Microbridge Mass Airflow Sensor (available from Honeywell Corp., Minneapolis, Minn.). - Another feature of the
preferred respiration sensor 40 is the ability to sense bidirectional flow, i.e., flow in each direction through thesensor 40. It is preferred that the flow generated by inhaling causes a voltage output of one polarity from thesensor 40, while flow generated by exhaling causes an output voltage of the opposite polarity. In any event, it is preferred that thesensor 40 be capable of detecting both inspiration and expiration. - In addition to the preferred flow sensor, it should be understood that other types of sensors may be utilized to detect variations in respiration, preferably inhalation and exhalation. Those skilled in the art will recognize that pressure transducers, thermistors or infrared detectors may all be used to sense inhalation. In one example, a pressure transducer with the appropriate sensitivity, such as a solid-state piezoresistive, capacitive or electromechanical device, could be used to generate an electrical signal in response to the breathing cycle. In another example, thermistors could be used to detect changes in airflow due to respiration. If the thermistor was sufficiently sensitive, one may be able to ascertain the onset of inhalation by monitoring the temperature of a thermistor (or thermocouple) placed near the nostril. A flow measurement may also be possible with the use of two thermistors in an anemometer configuration. Infrared detectors, such as single element bolometers, could be used as well if they possess the speed and accuracy to distinguish variations in respiration.
- The
respiration sensor 40 provides a signal to the respiration sensor/valve controller 42 which compares the signal to a predetermined reference level. The respiration sensor/valve controller 42 identifies the onset of inhalation by triggering when the sensor signal reaches the predetermined reference level. The respiration sensor/valve controller 42 then provides a signal to position the spool ofvalve 26 so oxygen flows fromsupply 20 topatient 16 via supplementaloxygen delivery device 18. The spool of thevalve 26 remains in this position for a period of time, the “dose time” (D), as specified by thesystem controller 10. In this manner, a dose of oxygen of duration D can be provided when the patient is inhaling. - One
preferred valve 26 of the embodiment ofFIG. 2 is a three-way, two-position, solenoid-actuated spool valve having threeports Common port 26 a is connected to the in vivo respiratory system of the patient 16 by the supplementaloxygen delivery device 18. Normally closedport 26 b is connected to theoxygen source 20 and normallyopen port 26 c is connected to respiration sensor 40 (with the other end of the preferred respiration sensor left open to atmosphere). Onepreferred valve 26 is manufactured by The Lee Company, of Westbrook, Conn., Model HDI LHDA0523111H. - When oxygen is not being supplied to the
patient 16, the spool of thevalve 26 is positioned such thatcommon port 26 a and normallyopen port 26 c are connected so that therespiration sensor 40, supplementaloxygen delivery device 18, andpatient 16 are in fluid communication, corresponding to the OFF position of thevalve 26. This allows the respiratory effort of the patient 16 to be detected by therespiration sensor 40, through the monitoring of the flow generated in the supplementaloxygen delivery device 18 by inspiratory and expiratory efforts. - To supply oxygen to the
patient 16, the spool of thevalve 26 is moved so as to connectcommon port 26 a and normally closedport 26 b, corresponding to the ON position of thevalve 26. This, in turn, allows for flow of respiratory oxygen to the patient 16 fromsupply 20 through thevalve 26 and the supplementaloxygen delivery device 18. - The ON period for the
valve 26, corresponding to the dosage period as discussed below, is preferably shorter than the inhalation period for the patient. As a result, the patient may often be inhaling after thevalve 26 is OFF (i.e., closed). To reduce or prevent multiple openings of thevalve 26 during a single inhalation, it is preferred that thevalve 26 remain closed until thesensor 40 detects the onset of exhalation. Once exhalation is detected based on thesensor 40, the system can then resume monitoring for the onset of inhalation, whereupon the cycle is repeated. - Because the
preferred valve 26 is a 3-port valve, there is a short period after opening or closing thevalve 26, (the “bounce period”) where the sensor output voltage spikes or bounces due to oxygen leaking from the normally closedport 26 b to the normallyopen port 26 c while the valve spool is still moving. Once thevalve 26 is fully ON or OFF and the valve spool has stopped moving, the bounce signal disappears. It is preferred that monitoring of therespiration sensor 40 be adjusted to avoid false readings due to the bounce signal after turning the valve 260N or OFF. This adjustment can take the form of a delay in monitoring the signal provided by thesensor 40 after moving thevalve 26 between the ON and OFF positions until the bounce signal has passed. - In some systems, the bounce signal may be monitored and used advantageously. The bounce signal (whether generated during ON or OFF movement of the valve spool) may be used to detect the presence of oxygen at the
supply 20. No bounce signal may indicate that no oxygen is present because of the lack of pressurized oxygen at normally closedport 26 b. In the preferred embodiment, the bounce signal generated by turning thevalve 26 to the OFF position (i.e., closingport 26 b) is used for this check because that bounce signal is typically larger and longer in duration than the bounce signal generated by turning thevalve 26 to the ON position (i.e., openingport 26 b). - Another advantage of the 3-
port valve 26 is that sensor's zero-flow offset voltage can be checked while thevalve 26 is in the ON position. The measured sensor offset voltage signal (Vo) can be used to generate a correction for drift in the sensor offset voltage. After thevalve 26 has been ON longer than the valve-ON bounce period, the signal from therespiration sensor 40 can be read and recorded for use in, e.g., a software-generated correction for zero-flow sensor offset voltage. This sensor offset voltage signal is obtained from therespiration sensor 40 when thevalve 26 is ON because no flow is to be expected through therespiration sensor 40 under those conditions (port 26 c is closed). In addition, if this offset reading is greater (in absolute value) than a predefined upper limit (VoMAX), this can be used to indicate eithersensor 40 orvalve 26 failure; e.g., thesensor 40 has drifted too far out of specification, thevalve 26 is leaking, thevalve 26 is stuck in the OFF position, etc. - The
demand delivery module 12 described above is a subsystem that communicates to and receives communication fromsystem controller 10. In the described methods, it receives continually updated values of the dose time D. It will be understood, however, that those skilled in the art could design ademand delivery module 12 which is more or less dependent on thesystem controller 10 than is described in this embodiment. For example, it may be desirable to construct a system whererespiration sensor 40 provides a signal directly to thesystem controller 10 with no separate respiration sensor/valve controller 42 being provided. Thecontroller 10 would then provide a control signal tovalve 26 directly as well as perform the other operations that are described as being performed by the respiration sensor/valve controller 42. - Moreover, it should be understood that alternative designs for the connections of the
valve 26,respiration sensor 40,oxygen source 20, andpatient 16 may be envisioned by the those skilled in the art. It would be possible to design a system in which an in-line flow sensor and/or three-port, two-way valve are not required. For example, the designs may involve a plurality of valves and sensors. It should be understood that the methods and systems of the described device operate independently from the specific configuration of hardware used for sensing variations in respiration and the specific valve configuration used to control the flow of oxygen. - Although the
demand delivery module 12 described above is used to control delivery of supplemental oxygen to a patient from thesource 20, thedemand delivery module 12 and the methods of operating it as described above could find wider application. For example, they could be used in connection with critical care systems in which FiO2 is to be controlled via the use of masks or other delivery devices used in connection with, e.g., respirators, ventilators, BIPAP (Bilevel Positive Airway Pressure) systems, etc. As a result, the demand delivery module and methods of operating it are not to be limited to use in connection with systems and methods of delivering supplemental oxygen as part of a sub-acute care regime. - As long as the data stream from the blood
oxygen content sensor 14 is valid (as described in detail below), thecontroller 10 can use the data to control delivery of oxygen to the patient. The feedback control can be implemented as a portion of software code contained in thecontroller 10; however, it could alternatively be a hard-wired controller or combination of hardware and software in other embodiments. - There exist a variety of control methods that are of utility in the present method and invention. The goal of any control method is stable operation of the controlled system about a setpoint or desired value. In the preferred embodiment, the desired value is a blood oxygen saturation (SpO2) of 90%. One control algorithm, the ON/OFF method, is diagrammed in
FIG. 3 a. This diagram assumes that the data generated by the blood oxygen content sensor is valid (validity and invalidity of that data is discussed in more detail below). - The system measures the patient's blood
oxygen content level 100. With that information, adecision 102 is made. When the measured blood oxygen content level is not below the desired value no oxygen is delivered 104. When the measured blood oxygen content level is below the desired value, oxygen is delivered 106. For example, when the measured blood oxygen content level is not below the desired value,controller 10 sets a dose time of zero (D=0), thereby preventing the delivery of supplemental oxygen. Alternatively, the system may otherwise restrict the flow of oxygen by, e.g., reducing its flow to a very low value in an attempt to conserve the supplemental oxygen source. The reduction in flow can be accomplished using a variable flow valve or by introducing a flow restrictor into the system between thesource 20 and thepatient 16. When the measured blood oxygen content falls below the desired value,controller 10 delivers supplemental oxygen to thepatient 16 by, e.g., setting a non-zero value (D>0) for the dose time or otherwise increasing the flow of oxygen to the patient. - As long as the measured blood oxygen content level remains below the desired value, the system provides oxygen when the patient is inhaling. In one relatively simple implementation, the “ON” dose time D could be very long. Preferably, however, the dose time is equal to or shorter than a typical inhalation period, in which case one or more pulses of duration D of oxygen are delivered during inhalation. This ON/OFF control approach is analogous to the operation of a furnace using a mercury switch thermostat, i.e., oxygen delivery is either ON or OFF.
- The feedback control algorithm may alternatively use a Proportional-Integral-Derivative (PID) loop as illustrated in
FIG. 3 b. Other embodiments could use algorithms based on fuzzy logic, look-up tables, P or PI loops or increment/decrement methods (oxygen delivery that increases or decreases in a preprogrammed fashion relative to setpoint and/or trend). The PID algorithm is fundamentally different from the simple ON/OFF control algorithm in that it uses both the current value of the blood oxygen content and also trend information to determine whether the patient needs supplemental oxygen and, if so, how much oxygen should be delivered when the patient is inhaling. Because of the use of trend information, a system controlled with a PID loop will, at times, deliver oxygen to the patient even if their blood oxygen content is above the desired value; or, at other times, it may not deliver oxygen even if they are below the desired value. An example of when this might occur is when the patient's blood oxygen content was above the desired value, but was also dropping very quickly. In this case, the PID loop would start oxygen delivery before the blood oxygen content actually fell below the desired value. (The ON/OFF method would not start oxygen delivery until after the blood oxygen content was below the desired value). This may allow a PID control method to more effectively reduce the fluctuations of the blood oxygen content about the desired value. - A simplified flow diagram of one such PID control system is illustrated in
FIG. 3 b where the data stream of the measured blood oxygen content level sensor is assumed to be valid (validity/invalidity of that data is discussed in more detail below). The system measures the patient's bloodoxygen content level 110. The current information is compared withearlier data 112 to determine how much oxygen (i.e., a variable dose), based on the parameters of thePID loop 114, should be delivered to the patient 1116. In some instances, the parameters of the PID loop indicate that no oxygen is to be delivered 118, and in other instances some variable dose of oxygen will be delivered based on the parameters of the PID loop. - The preferred systems for implementing the methods of the present invention use a digital controller. As a result, discretization of the following continuous-time PID control equation must be performed:
D(t)=K p *[e(t)+(1/T i)*∫e(t′)dt′+(T d)*de/dt] (1)
where D(t) is the oxygen dose time at time t, Kp is the loop proportional gain, Ti is the integral time, Td is the derivative time, and where the integral is integrated over the range of from zero to t. The preferred embodiment utilizes a first order discretization of the continuous time PID equation. This can be seen in Equation 2,
D(t n)=D(t n-1)+A 0 e(t n)+A 1 e(t n-1)+A 2 e(t n-2) (2)
where D(tn) is the control signal (oxygen dose time) generated for time period tn, e(tn) is the difference between the desired level of blood oxygen saturation (the setpoint) and the measured level at time tn. The coefficients, A0, A1, and A2 are given by Equations 3-5 below:
A 0 =K p*(1+t n /t i +t d /t n) (3)
A 1 =−K p*(1+2*t d /t n) (4)
A 2 =K p*(t d /t n) (5)
where Kp is the loop proportional gain, ti is the integral time, td is the derivative time and tn is the period of the measurement (one second if using the preferred oximeter). - As mentioned, the quantity e(tn) is the difference between the SpO2 value at time tn and the desired value. In one embodiment, a fixed setpoint of SpO2=90% is used for the desired value. The control algorithm will specify doses of oxygen in order to maintain the blood oxygen saturation at this level. It is thought that this saturation level may provide the necessary correction to the patient's hypoxemia, while at the same time conserving the greatest amount of oxygen. It should be apparent to those skilled in the art that the desired value (setpoint) can be changed to achieve different therapeutic and economic goals.
- Moreover, a system that uses additional physiological parameters, such as pulse rate or respiratory rate, in addition to blood oxygen content as determined by the oxygen sensor to determine a target blood oxygen level (setpoint) that changes on a rolling basis could also be implemented. For example, one may use the heart rate to monitor the patient's activity level and therefore anticipate increased or decreased need of oxygen and adjust the setpoint accordingly. Such schemes would be seeking to ameliorate the possible increased/decreased hypoxemia caused by a change in physical activity level. Such changes to the setpoint should be considered to be within the spirit and scope of the present invention.
- Referring now to Equations 3-5 above, the transfer function coefficients A0, A1 and A2 are determined by the settings of loop proportional gain Kp, the integral time ti, the derivative time td and the time between data points tn. The determination of these values will typically be accomplished through clinical monitoring of COPD patients while the system is in use. The specific values of these loop parameters will depend on design goals such as loop stability, overshoot, time-to-achieve-control, and accuracy. Methods for obtaining values which provide for effective operation of the control loop will be known to those skilled in the art.
- In one method, the control signal D(tn) is the dose time needed to maintain the blood oxygen level at the desired value. The dose time signal is provided by
controller 10 to respiration sensor/valve controller 42. It is the duration of time thatvalve 26 will be held in the ON or open position which permits oxygen to pass fromsupply 20 to patient 16 (via the supplementaloxygen delivery device 18 illustrated inFIGS. 1 and 2 ). A dose of oxygen of duration D(tn) is provided during inhalation (as indicated byrespiration sensor 40 and sensor andvalve controller 42, described previously). - It should be understood that other methods besides varying the dose time could also be employed to control the patient's blood oxygen content. For example, a system which includes a variable-flow valve (as opposed to the preferred open/closed valve) could be constructed. In such a system, the
controller 10 could specify the oxygen flow level. The specified flow could, in turn, be provided for a fixed period of time at the onset of each breath, or continuously. During those times in which the patient does not require supplemental oxygen and/or is not inhaling, the flow could be restricted to a low level or to zero followed by periods in which the flow is higher (when the patient is in need of supplement oxygen and is inhaling). - Alternately, the blood oxygen content could be controlled by providing a dose of oxygen on one or more sequential breaths and then delivering no oxygen on one or more subsequent breaths. In this method, the control parameter could be described as the number of breaths during which oxygen is or is not delivered. It should be understood that those skilled in the art could construct a control scheme which uses any of these alternate methods or a combination of these methods.
- The
controller 10 also may include a minimum limit (Dmin) for the dose time. If the dose time D(tn), as determined by Equation 2, is less than Dmin, a dose time of Dmin will be used instead. In one embodiment, Dmin will be zero. The dose time D(tn) determined by Equation 2 will, at times, be negative. This will primarily occur when the patient's blood oxygen content is greater than the desired value. Since a negative dose time is not physically meaningful, the controller will instead substitute a dose time of Dmin. Of course, Dmin could also be greater than zero. - Similarly, in one embodiment the
controller 10 would also have a maximum limit (Dmax). If the dose time D(tn), as determined by Equation 2, is greater than Dmax, a dose time of Dmax is used instead. In one embodiment, Dmax is equal to twice the default dose (described in detail below). This prevents the application of excessive amounts of oxygen and thus minimizes the patient's risk of hypercapnia (carbon-dioxide retention). Those skilled in the art will appreciate that other values of Dmax could also be used. - In another embodiment, the
controller 10 could include an “anti wind-up” provision. Because the dose time may have minimum and maximum limits (Dmin and Dmax, described above), it may be advantageous to include an anti wind-up provision to prevent the integral portion of the PID-calculated dose time from getting too large or too small. One way this could be implemented is as follows: If the previous PID-calculated dose time D(tn-1) (from Equations 2-7) is less than Dmin or greater than Dmax, the integral term from Equation 3 is deleted (i.e., Equation 3 is replaced with Equation 3a, below):
A 0 =K p*(1+t d /t n) (3a) - In systems and methods according to the present invention, the ability to respond to periods of invalid or bad data in the blood oxygen content measurements is preferably provided. In the preferred methods and systems, the delivery of oxygen moves from the closed loop control described herein to open loop control based on the criteria described herein (i.e., default values, interpolated data, etc.) and back to closed loop control when the blood oxygen measurements are again valid.
FIG. 4 illustrates these concepts. As shown, the system obtains a measured bloodoxygen content level 120. A decision is then made as to whether the measured blood oxygen content level data is valid or invalid 122. The system may determine whether the measured blood oxygen content level data is invalid on a point-by-point basis or it may determine whether the data stream (including a plurality of data points) is invalid as discussed below. Regardless, a decision will be made as to whether the measured blood oxygen content level data is valid. If the measured blood oxygen content level data is invalid, the system will deliver a default amount of oxygen to thepatient 124. If the measured blood oxygen content level data is valid, the system will deliver oxygen to thepatient 126 according to the appropriate control algorithm (ON/OFF, PID loop, etc.). - In other words, the methods/systems according to the present invention will determine when the blood oxygen content data is invalid, deliver a default amount of oxygen during periods of invalid data, and then resume delivery of supplemental oxygen based on blood oxygen content when that data is again valid. The ability of the systems and methods of the present invention to move from closed to open and back to closed loop control provides a robust system that can operate with a minimum of supervision from medical personnel. Those qualities are essential in any system designed for residential or ambulatory use by sub-acute patients.
- The following description illustrates some preferred methods for accomplishing these features, but it should be understood that in its essence the present invention provides for that movement from closed loop control to open loop control and back to closed loop control based on the presence of valid or invalid blood oxygen content measurements.
- In one embodiment, before the measured blood oxygen saturation reading (Sp02) is used for determining the dose time D of oxygen to be delivered to the patient 16 from the
oxygen source 20, various error handling and artifact detection procedures are followed to prevent erroneous over- or under-dosing of oxygen to the patient. In one embodiment of the present invention, the error flags provided by theoxygen sensor 14 in the serial data stream are combined with a numerical analysis of the Sp02 data to create an artifact detection and handling scheme. - The serial data stream of the preferred
pulse oximeter 14 provides one data point per second. Each data point includes three bytes of information, as follows:1st byte = Status Bit 7 = Always set to “1” Bit 6 = Sensor disconnected, set if true Bit 5 = out of track, set if true Bit 4 = low perfusion, set if true Bit 3 = marginal perfusion, set if true Bit 2 = bad pulse, set if true Bit 1 = heart rate bit 8 Bit 0 = heart rate bit 7 2nd byte = Heart Rate (511 = bad data) Bit “7” is always set to “0” Heart Rate Data = Bits 0-6 Plus bits 0 & 1 of status byte to provide 9 bits of resolution 3rd byte = SpO2 (127 = bad data) - The first byte of the data point may include error flags for some problems associated with pulse oximetry. These flags are examined for the occurrence of a disconnected sensor, low or marginal perfusion, out of track oximeter and bad pulse. If any of these flags are set, the accompanying SpO2 and heart rate data is considered bad. If the data point is determined to be bad, a timer (Timer1) is started by the controller 10 (unless it is already running based on an earlier bad data point) which then waits for the next data point. The function of Timer1 is to track the cumulative time over which consecutive bad data points are being received. Timer1 is stopped and reset to zero each time a valid or good data point is received.
- If, however, none of the flags is set, a second error check may be performed using a statistical analysis of the data. The new data point is compared to a mean value of previous data points which represents the patient's current blood oxygen content. The details of the calculation of this mean value are described below. The current data point is subtracted from the mean value to generate a difference, ΔSpO2 in %. (For the data-validity analysis below, if ΔSpO2 is less than zero, its absolute value is used.)
- If the absolute value of ΔSpO2>4% and Timer1 equals zero (i.e., the last data point was valid), then the current data point is determined to be invalid. Since the time between data points in the serial data stream will be about one second, a change larger than 4 percent in the SpO2 in such a short time would be physiologically impossible. If the data point is determined to be invalid using this procedure, the data is ignored, Timer1 is started and
controller 10 waits for the next data point. - If, however, the absolute value of ΔSpO2>4% and Timer1 does not equal zero, then additional evaluation may be performed. The observed rate of oxygen desaturation in humans can approach 20%/minute or about 3% every 10 seconds. If Timer1 is less than 10 seconds and the absolute value of ΔSpO2>4%, then the data is considered to be invalid. If Timer1 is greater than 10 seconds, but less than 20 seconds then the acceptance criteria is absolute value of ΔSpO2 less than 8% for the data to be valid. If Timer1 is greater than 20 seconds, but less than 30 seconds then the acceptance criteria is absolute value of ΔSpO2 less than 12%. If Timer1 is greater than 30 seconds, then oxygen is delivered using the default method which is described in detail below. It should, of course, be understood that, in the above analysis, the specific values of 4%, 8%, and 12%, and the specific times of 10, 20 and 30 seconds could be replaced with different values.
- Some alternate criteria for identifying when individual data points are invalid or bad could include, but are not limited to, identifying an invalid data point when: (a) the SpO2 value is outside upper and/or lower limits (e.g., a lower limit of about 70% and/or an upper limit of about 98%); or (b) the heart rate is outside upper and/or lower limits (e.g., a lower limit of about 40 beats per minute and/or an upper limit of about 200 beats per minute).
- If the data point passes all the tests, Timer1 is stopped and set to zero (if necessary) and the new mean value of blood oxygen content is calculated with the most recent data point. The new mean value is then compared to the setpoint and a dose time D is calculated as detailed above in Equations 2-5.
- In one embodiment, an exponentially-weighted arithmetic mean of the previous data points is used to represent the current blood oxygen content. The new mean is calculated as follows:
new mean=(current data point)*W1+(previous mean)*W2 (6)
where
W1=1−exp(−Δt/T) W2=exp(−Δt/T). (7)
Here Δt is the time between data points (one second using the preferred oximeter), and T is a parameter which represents an appropriate time scale for the averaging. If an appropriate value of T is chosen, the exponentially-weighted mean will smooth out normal point-to-point “noise” fluctuations in the pulse oximeter data without masking the real trends related to the patient's blood oxygen content. (A typical value would be T=10 seconds, although other values could be used.) - Other methods could also be used to determine a mean value that is representative of the patient's current blood oxygen content. For example, a harmonic, or geometric mean might be used. (Descriptions of these types of means can be found in “Standard Mathematical Tables” by CRC Press, 24th edition, pages 470-471.) Alternately, a “running” mean might be used. In this method, the mean of a fixed, predetermined number of the most-recent data points could be used. For example, with the preferred pulse oximeter which delivers one data point per second, one could average the preceding 10 data points, thus calculating a mean which represents the patient's blood oxygen content for the previous 10 seconds.
- In one embodiment, the dose time D of oxygen that is delivered to the user may depend on the validity of the data stream from the oxygen sensor. If the time over which the consecutive invalid or bad data points are received, as indicated by Timer1, exceeds a predetermined, physiologically-relevant time scale for patient desaturation (referred to as Desattime), alternative, “default” oxygen delivery procedures are employed. In one embodiment Desattime is equal to 30 seconds. The default assumption is that a patient is always in need of oxygen, unless the blood oxygen content sensor positively indicates that they are not.
- If the current oxygen sensor data point is invalid, but Timer1 is less than Desattime, the oxygen dose time D may remain unchanged from its current value. The system will provide a dose of this duration at the onset of inhalation. The process of gathering and evaluating blood oxygen saturation data then continues. Prior to the onset of invalid data, the system was either administering oxygen to correct a deficiency or the patient was in no need of oxygen. Thus, in this embodiment it is assumed that the patient's oxygen needs have not changed during this short time of invalid data and the status quo is maintained. If the patient was receiving no oxygen prior to the invalid data (e.g., dose time D=0), the system will not administer any oxygen. If, however, the patient was receiving oxygen (e.g., D>0), the system will typically continue to administer the same dose by responding to inhalation as described above. This will preferably continue until either a valid data point is received and a reevaluation can be made of the patient's condition or Timer1 exceeds Desattime.
- If the oxygen sensor data points continue to be invalid and Timer1 exceeds Desattime, then the device will default to another oxygen delivery method. In the default method, the
controller 10 will default to administering a prescription-equivalent dose of oxygen to the patient 16 from theoxygen source 20 via thedemand delivery module 12. This default dose of oxygen could take many forms: In one embodiment, the default could be a continuous flow of oxygen. To implement this, the system could output a very large dose time to holdvalve 26 in the ON position which allows oxygen to flow fromsource 20 topatient 16. Alternately, in the preferred embodiment, the default mode would provide a short dose of oxygen (of duration D=Ddefault) at the onset of inhalation for almost every breath. In this preferred embodiment, Ddefault would be shorter than a typical inhalation period, in which case the system would provide pulses of duration Ddefault synchronized with each inhalation (demand mode). This will continue until such time as the blood oxygen content data is valid and closed-loop control over oxygen delivery can start anew. - It is possible to envision additional alternate methods of default flow. In one such alternate embodiment, the valve does not necessarily open with each and every breath. It should be understood that these alternate methods of implementing a default flow still fall within the scope of the present invention. The object of the default method is to provide a total flow of oxygen during this period of default operation that is no less than the physiological equivalent amount that is prescribed to the patient by the physician. (Physiological equivalence meaning the amount dispensed by other demand delivery devices to provide adequate oxygen therapy.) It should be understood that the notion of physiological equivalence as regards demand delivery devices will change over time as their effects on the physiology of COPD patients is better understood by the medical community. Current practice indicates that 35 ml delivered every other breath at the beginning of inhalation is equivalent to a continuous flow of 2 liters/minute of pure oxygen.
- In one embodiment of the invention, the duration of the default dose (Ddefault) may be set by the patient's respiratory therapist using a hardware switch on the
user interface 32 that is not accessible to the patient. Other techniques of setting the pulse width may be possible, such as a remote controllers, push buttons, etc. - Also, in one embodiment, if Timer1 exceeds Desattime, then the previous mean value of the blood oxygen saturation is reset and data acquisition starts anew. In this way, it is assumed that the old SpO2 information is no longer valid for the patient's current physical state and that to properly administer oxygen a more current measure of the blood oxygen level is needed. Thus, by using Timer1, a period of invalid data that exceeds Desattime will always lead to the administration of oxygen to the patient. This will correct any undetected desaturation events. Moreover, the
controller 10 will always use the most current, valid information regarding the patient's blood oxygen level. - It should also be understood that other methods for recognizing and handling erroneous data points from the oxygen sensor could be devised. Those skilled in the art could create different algorithms for handling invalid data points, such as replacement of invalid data points with interpolated values based on the recent trend in the blood oxygen saturation. Alternative methods of identifying and rejecting invalid data points should be considered to be within the scope of the present method and system.
- Another method for determining whether the oxygen sensor data is valid or invalid can be based on the data stream (a plurality of data points) rather than the individual data points. For example, instead of tracking the time since the most recent valid data point or points, the system could instead determine if the data stream is valid or invalid by comparing the number of valid data points in a “look-back” window (for example, the 60 to 100 most recent data points) to a preset minimum threshold. If the number of valid data points in the look-back period is greater than or equal to the specified minimum, the data stream is considered to be valid and the calculated dose is delivered; if the number of valid data points is less than the minimum, the default dose is delivered.
- Those skilled in the art will understand that a wide range of possibilities for oxygen delivery in default mode beyond those that have been described here could be used. Although they are not described in detail herein, they should be considered as falling within the scope of the methods according to the present invention.
- If invalid data is a problem, the
controller 10 may be used to notify the patient of a problem with the pulse oximetry via theuser interface 32 and/oralarm 38. This notification may take the form of a warning light, readout, buzzer or some combination of these. Those skilled in the art may also conceive of other methods of warning the user that are not detailed herein. After the warnings have been issued and default demand flow mode entered, thecontroller 10 resumes monitoring the output of the oxygen sensor for valid data. - Along with monitoring the breathing cycle for oxygen delivery, the invention makes provision for the detection of apnea, the cessation of breathing for a prolonged period of time. Timer2 starts each time an inhalation is detected. If the elapsed time between breaths is greater than a predetermined time, e.g., 15 seconds, as determined by Timer2, then the
alarm circuit 38 is activated by thecontroller 10 to signal the patient of a possible apneic event. These alarms preferably stop sounding upon detection of the next inhalation. - Other alarms and indicators that can be included in the systems and methods of the present invention include hypoxia alarms, high respiration rate alarms, high/low pulse rate alarms, and patient monitoring indicators. These alarms and/or indicators can be used to warn the patient that their supplemental oxygen equipment is not operating properly, they are not using it properly, or they are having other problems and need to seek medical treatment.
- In the case of an hypoxia alarm, the patient could be provided with a visible and/or audible alert when their blood oxygen saturation level has been below a healthy level for a period of time—even though they have been using the above-described device. This condition could be caused, e.g., by a malfunctioning of the supplemental oxygen equipment or a worsening of the patient's respiratory condition. In normal operation of the preferred embodiment as described above, the device would increase the dose time D(t) in response to the patient's hypoxia, up to a preset upper-limit dose time Dmax. It is possible that the patient's condition could have worsened so much so that even this maximum dose is not sufficient to keep their blood oxygen saturation at a healthy level. It would be advantageous to alert the patient to this condition so they may seek appropriate medical attention. This could enable earlier detection and treatment of potentially dangerous and costly health conditions.
- The hypoxia alarm could be implemented in software, hardware, or in a combination of software and hardware. In the methods described above, the
controller 10 may already calculate a mean value of blood oxygen content from the valid blood oxygen saturation data points. In the preferred embodiment, the mean value that is already calculated is an exponentially-weighted arithmetic mean with a typical time constant T=10 seconds. This mean represents the average blood oxygen saturation for the previous 10 seconds. For the hypoxia alarm, a second mean value of blood oxygen saturation, for a longer period (e.g. T=1 hour) could be calculated in an analogous manner. In the preferred embodiment, this hypoxia alarm mean would also be an exponentially-weighted mean because it eliminates the need to store each of the many data points that would be collected over the longer period, thereby decreasing the memory requirements. - It should be understood, however, that other methods of calculating a mean as discussed above could also be used. When the second mean falls below a preset limit representing the lower limit for healthy blood oxygen levels (e.g., 88%),
controller 10 could alert the patient viaalarm circuit 38. In the preferred embodiment, the time period for the second mean is 1 hour, and the lower limit for blood oxygen saturation is 88%; however, it should be clear that other values could be used for these parameters. - In the case of a high respiration rate alarm, the patient could be provided with a visible and/or audible alert when their respiration rate has been above a healthy level for a period of time. Some patients with respiratory diseases will compensate for an impaired respiratory system by maintaining a higher than normal breathing rate. These patients can sometimes maintain a healthy blood oxygen saturation, but over the long term, the increased respiration rate is also detrimental to their health. The onset of a period of increased respiration rate could be caused by a malfunctioning of the supplemental oxygen equipment or a worsening of the patient's respiratory condition.
- In normal operation of the preferred embodiment as described above, the device increases the dose time D(t) in response to the patient's hypoxia. It is possible that the patient's condition could have worsened, but the patient is compensating by breathing at a higher rate. As with hypoxia, it would be advantageous to alert the patient to this condition so they may seek appropriate medical attention.
- This alarm could be implemented in software, hardware, or in a combination of software and hardware. The system described above already measures the elapsed time between each breath via Timer2. For the high-respiration rate alarm, a mean value of the elapsed time between each breath could be calculated in a manner analogous to the mean blood oxygen levels. In the preferred embodiment, this mean would also be an exponentially-weighted mean. It should be understood, however, that other methods of calculating a mean as described above could also be used. When the mean elapsed time between breaths falls below a preset limit corresponding to the upper limit for healthy respiration rates (e.g., minimum elapsed time of two seconds, corresponding to a breathing rate of 30 breaths per minute), the system could alert the patient via
controller 10 andalarm circuit 38. In the preferred embodiment, the time period for calculating the mean is 1 hour, and the lower limit for elapsed time between breaths is 2 seconds (30 breaths per minute); however, it should be clear that other values could be used for these parameters. - In the case of a high/low pulse rate alarm, a visible and/or audible alert could be provided to the patient when their pulse rate has been above or below healthy levels for a period of time. Excessively high or low pulse rates could be an important indication that the patient needs medical treatment. It would be advantageous to alert the patient to these conditions so they may seek appropriate medical attention.
- In the preferred embodiment, these alarms would be implemented in software, hardware, or in a combination of software and hardware. The preferred oxygen sensor typically provides pulse rate data (in addition to blood oxygen data). A mean pulse rate could be calculated in a manner analogous to the calculation of other means, described above. As with the other alarms, in the preferred embodiment, this mean would also be an exponentially-weighted mean or, alternatively, other means or averages could be used.
- When the mean pulse rate falls above or below preset limits (e.g., less than 40 or above 180 beats per minute), the system could alert the patient via
alarm circuit 38. In the preferred embodiment, the time period for the mean is 20 minutes, the lower limit for pulse rate is 40 beats per minute, and the upper limit for pulse rate is 180 beats per minute; however, it should be clear that other values could be used for these parameters. - Among the indicators that could be provided include various patient and equipment monitoring functions. In the preferred embodiment, these indicators could be implemented in software, hardware, or in a combination of software and hardware. The information provided by these indicators could be useful to the patients, respiratory therapists, physicians, etc. Some examples of indicators are described below.
- One indicator that could be useful is an “ON-time” indicator. An important factor in treating patients that require supplemental oxygen is monitoring their compliance with their oxygen prescription. Some patients will not use their oxygen equipment as much as they should. Medical studies have shown that most patients must use their supplemental oxygen equipment at least 18 hours per day in order to receive significant benefits from it. The ON-time parameter would indicate the total amount of time that the device has been powered ON (analogous to the “hour meter” found on most oxygen concentrators), thus giving an indication of the total time the equipment was used since the ON-time parameter was last reset to zero. In the preferred embodiment, a timer would be started by
controller 10 each time the unit was turned ON. When timer reached a value of, e.g., one minute,controller 10 would increment a non-volatile memory location and reset and restart the timer. In this manner, a memory location associated with the ON-time timer would count the number of minutes the apparatus had been powered ON. The memory location associated with the ON-time timer would preferably be non-volatile and, as a result, the total minute count would be retained while the unit was powered OFF. When powered ON again, counting would resume from the previously accumulated value. In the preferred embodiment, the ON-time timer could be accessed and reset via theuser interface 32. - It may also be useful to track the total number of times each alarm condition has occurred. In the preferred embodiment, a separate non-volatile memory location would be used to count the number of times each alarm condition had occurred. Each time an alarm condition occurred, the associated memory location would be incremented. In addition to the three alarms described above, the preferred embodiment could also count the number of apnea alarms. The various alarm-count parameters could be accessed and reset, e.g., via the
user interface 32. - It may also be useful to keep track of the total amount of time the unit was in “default” mode as described above. In a manner similar to tracking ON-time, the default time monitor would preferably consist of a non-volatile memory location that would be incremented each time the timer reached one minute and the unit was in the default mode. In a similar manner, a feedback-control-time parameter could be calculated (although this parameter may be more easily obtained by subtracting the default time from the ON-time). As with the other monitored parameters, default time would preferably be accessed and reset via the
user interface 32. - It may also be useful to keep track of the total number of times the apparatus entered the “default” mode. In the preferred embodiment, a separate non-volatile memory location would be used to count the number of times the default delivery condition had occurred. Each time the apparatus entered the default delivery mode, the associated memory location would be incremented. The default count parameter would preferably be accessed and reset via the
user interface 32. - It may also be useful to keep track of the total amount of time the patient was hypoxic (e.g., SpO2<88%). In a manner similar to tracking the ON-time, the hypoxic-time monitor would consist of a non-volatile memory location that would be incremented each time the timer reached one minute and the patient was hypoxic (and the SpO2 data was deemed valid). As with the other monitored parameters, hypoxic-time could be accessed and reset via the
user interface 32. - It may also be useful to keep track of the average duration of the pulses of oxygen that are provided at each inhalation (i.e., the average dose time). The average-dose-time parameter could provide a useful indication of the amount of supplemental oxygen that was required to keep the patient's blood properly oxygenated. Trends in this parameter could be useful for tracking the overall efficiency of the patient's respiratory condition. For example, a measurable increase in the average-dose-time (i.e., an increase in the amount of supplemental oxygen needed) could indicated a worsening of the patient's condition, and thus provide an early warning allowing the patient to seek medical attention before their condition required a costly hospitalization.
- In the preferred embodiment, two nonvolatile memory locations would be used to calculate average-dose-time: a counter and an accumulator. Each time, e.g., an inhalation was sensed, the current dose time (as indicated by controller 10) would be added to accumulator and the counter would be incremented. The average-dose-time could then be calculated by dividing the accumulator value by the counter value. As with the other monitored parameters, average-dose-time could be accessed and reset via the
user interface 32. - In addition to those parameters specifically recited herein, other useful parameters may also be generated. For example, average SpO2 (the patient's average blood oxygen saturation); average respiration rate; average heart rate; etc. Monitoring of these parameters could also be implemented in software, hardware, or in a combination of software and hardware.
- Various methods and systems for conserving supplemental oxygen delivery to a sub-acute patient based on continuous blood oxygen content measurements and inhalation have been described above. Many changes, alterations and variations of the subject invention will become apparent to those skilled in the art after consideration of this specification and the accompanying figures and diagrams of the preferred embodiments. For example, the values chosen for, e.g., ΔSpO2, Timer1, Timer2, etc., are intended to be exemplary of some preferred values and should not limit the scope of the invention unless the values are explicitly recited in the claims. All such changes, modifications, variations, etc. are deemed to be covered by the claims which follow.
Claims (28)
1. A method of controlling oxygen delivery comprising:
continuously measuring blood oxygen content of a patient to obtain a measured blood oxygen content level;
delivering oxygen from an oxygen source to the patient if the measured blood oxygen content level is below a desired value;
restricting the delivery of oxygen to the patient if the measured blood oxygen content level of the patient is above the desired value;
determining if the measured blood oxygen content level is invalid; and
delivering a default amount of oxygen to the patient if the measured blood oxygen content level is invalid.
2. A method according to claim 1 , wherein the oxygen is delivered through a nasal cannula.
3. A method according to claim 1 , further comprising determining when the patient is inhaling.
4. A method according to claim 1 , further comprising providing an alarm if the measured blood oxygen content level is invalid.
5. A method according to claim 1 , further comprising providing an alarm if the patient experiences hypoxemia.
6. A method of controlling oxygen delivery comprising:
continuously measuring blood oxygen content of a patient to obtain a measured blood oxygen content level;
delivering a variable dose of oxygen from an oxygen source to the patient, wherein the variable dose is at least partially determined based on the measured blood oxygen content level;
determining if the measured blood oxygen content level is invalid; and
delivering a default amount of oxygen to the patient if the measured blood oxygen content level is invalid.
7. A method according to claim 6 , wherein the variable dose of oxygen is at least partially based on a trend in measured blood oxygen content as measured at different times.
8. A method according to claim 6 , wherein the variable dose of oxygen is at least partially based on a difference between a desired value for the measured blood oxygen content and the measured blood oxygen content, and wherein the method further comprises changing the desired value for the measured blood oxygen content level.
9. A method according to claim 8 , wherein changing the desired value for the measured blood oxygen content level comprises monitoring the patient's heart rate and changing the desired value for the measured blood oxygen content level in response to change in the patient's heart rate.
10. A method according to claim 6 , wherein the variable dose includes a zero dose.
11. A method according to claim 6 , wherein the oxygen is delivered through a nasal cannula.
12. A method according to claim 6 , further comprising determining when the patient is inhaling.
13. A method according to claim 6 , further comprising providing an alarm if the measured blood oxygen content level is invalid.
14. A method according to claim 6 , further comprising providing an alarm if the patient experiences hypoxemia.
15. A method of controlling oxygen delivery comprising:
continuously measuring blood oxygen content of a patient to obtain a measured blood oxygen content level;
delivering a variable dose of oxygen from an oxygen source to the patient, wherein the variable dose is at least partially determined based on the measured blood oxygen content level;
determining if the measured blood oxygen content level is invalid; and
replacing the invalid measured blood oxygen content level with a value based on a recent trend in blood oxygen content level.
16. A method according to claim 15 , wherein the variable dose of oxygen is at least partially based on a trend in measured blood oxygen content as measured at different times.
17. A method according to claim 15 , wherein the variable dose of oxygen is at least partially based on a difference between a desired value for the measured blood oxygen content and the measured blood oxygen content, and wherein the method further comprises changing the desired value for the measured blood oxygen content level.
18. A method according to claim 17 , wherein changing the desired value for the measured blood oxygen content level comprises monitoring the patient's heart rate and changing the desired value for the measured blood oxygen content level in response to change in the patient's heart rate.
19. A method according to claim 15 , wherein the variable dose includes a zero dose.
20. A method according to claim 15 , wherein the oxygen is delivered through a nasal cannula.
21. A method according to claim 15 , further comprising determining when the patient is inhaling.
22. A method according to claim 15 , further comprising providing an alarm if the measured blood oxygen content level is invalid.
23. A method according to claim 15 , further comprising providing an alarm if the patient experiences hypoxemia.
24. A system for delivering respiratory oxygen to a patient, the system comprising:
a blood oxygen content level sensor;
a oxygen source;
a valve in fluid communication with the oxygen source;
a controller capable of operating the valve, the controller restricting oxygen flow through the valve when the blood oxygen content level measured by the blood oxygen content level sensor is above a desired value; and
means for determining when the blood oxygen content level measured by the blood oxygen content level sensor is invalid, wherein the controller operates the valve to deliver a default amount of oxygen to the patient when the measured blood oxygen content is invalid.
25. A system according to claim 24 , further comprising means for determining when the blood oxygen content level measured by the blood oxygen content level sensor is valid after being invalid, wherein the controller operates the valve to restrict oxygen flow through the valve when the blood oxygen content level measured by the blood oxygen content level sensor is above a desired value.
26. A system according to claim 24 , wherein the controller variably restricts oxygen flow through the valve to deliver a variable dose of oxygen from the oxygen source to the patient, wherein the variable dose of oxygen is at least partially determined based on the measured blood oxygen content.
27. A system according to claim 24 , wherein the controller determines the variable dose of oxygen at least partially based on a difference between a desired value for the measured blood oxygen content level and the measured blood oxygen content level.
28. A system according to claim 24 , wherein the controller determines the variable dose of oxygen at least partially based on a trend in measured blood oxygen content level as measured at different times.
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Cited By (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040206353A1 (en) * | 2003-04-21 | 2004-10-21 | Conroy John D. | System and method for monitoring passenger oxygen saturation levels and estimating oxygen usage requirements |
US20040206352A1 (en) * | 2003-04-21 | 2004-10-21 | Conroy John D. | System and method for monitoring passenger oxygen saturation levels and estimating oxygen usage requirements |
US20070271009A1 (en) * | 2003-10-30 | 2007-11-22 | Conroy John D Jr | System And Method For Monitoring Passenger Oxygen Saturation Levels And Estimating Oxygen Usage Requirements |
US20080216834A1 (en) * | 2007-03-09 | 2008-09-11 | Dan Easley | Method and Apparatus for Delivering a Dose of a Gaseous Drug to a Patient |
US20090241957A1 (en) * | 2008-03-27 | 2009-10-01 | Nellcor Puritan Bennett Llc | Breathing assistance systems with lung recruitment maneuvers |
US20090241956A1 (en) * | 2008-03-27 | 2009-10-01 | Nellcor Puritan Bennett Llc | Method for controlling delivery of breathing gas to a patient using multiple ventilation parameters |
US20100224191A1 (en) * | 2009-03-06 | 2010-09-09 | Cardinal Health 207, Inc. | Automated Oxygen Delivery System |
US20100224192A1 (en) * | 2009-03-06 | 2010-09-09 | Cardinal Health 207, Inc. | Automated Oxygen Delivery Method |
US20100313885A1 (en) * | 2009-06-16 | 2010-12-16 | Inspired Technologies, Inc. | Method of using a spool valve assembly for delivery of a gaseous drug |
US20100313888A1 (en) * | 2009-06-16 | 2010-12-16 | Inspired Technologies, Inc. | Spool valve assembly for delivery of a gaseous drug |
US20120017909A1 (en) * | 2008-09-23 | 2012-01-26 | Porges Charles E | Systems and methods for conserving oxygen in a breathing assistance device |
US8136527B2 (en) | 2003-08-18 | 2012-03-20 | Breathe Technologies, Inc. | Method and device for non-invasive ventilation with nasal interface |
US8381729B2 (en) | 2003-06-18 | 2013-02-26 | Breathe Technologies, Inc. | Methods and devices for minimally invasive respiratory support |
US8418694B2 (en) | 2003-08-11 | 2013-04-16 | Breathe Technologies, Inc. | Systems, methods and apparatus for respiratory support of a patient |
US8567399B2 (en) | 2007-09-26 | 2013-10-29 | Breathe Technologies, Inc. | Methods and devices for providing inspiratory and expiratory flow relief during ventilation therapy |
US8677999B2 (en) | 2008-08-22 | 2014-03-25 | Breathe Technologies, Inc. | Methods and devices for providing mechanical ventilation with an open airway interface |
US8770193B2 (en) | 2008-04-18 | 2014-07-08 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US8776793B2 (en) | 2008-04-18 | 2014-07-15 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and controlling ventilator functions |
US8925545B2 (en) | 2004-02-04 | 2015-01-06 | Breathe Technologies, Inc. | Methods and devices for treating sleep apnea |
US8939152B2 (en) | 2010-09-30 | 2015-01-27 | Breathe Technologies, Inc. | Methods, systems and devices for humidifying a respiratory tract |
US8955518B2 (en) | 2003-06-18 | 2015-02-17 | Breathe Technologies, Inc. | Methods, systems and devices for improving ventilation in a lung area |
US8985099B2 (en) | 2006-05-18 | 2015-03-24 | Breathe Technologies, Inc. | Tracheostoma spacer, tracheotomy method, and device for inserting a tracheostoma spacer |
US20150174359A1 (en) * | 2013-12-20 | 2015-06-25 | B/E Aerospace, Inc. | Pulse saturation oxygen delivery system and method |
US9132250B2 (en) | 2009-09-03 | 2015-09-15 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US9180270B2 (en) | 2009-04-02 | 2015-11-10 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive open ventilation with gas delivery nozzles within an outer tube |
US20160303405A1 (en) * | 2013-12-20 | 2016-10-20 | B/E Aerospace, Inc. | Pulse saturation oxygen delivery system and method |
WO2017192660A1 (en) * | 2016-05-03 | 2017-11-09 | Inova Labs, Inc. | Method and systems for the delivery of oxygen enriched gas |
US9962512B2 (en) | 2009-04-02 | 2018-05-08 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with a free space nozzle feature |
US10058668B2 (en) | 2007-05-18 | 2018-08-28 | Breathe Technologies, Inc. | Methods and devices for sensing respiration and providing ventilation therapy |
US10099028B2 (en) | 2010-08-16 | 2018-10-16 | Breathe Technologies, Inc. | Methods, systems and devices using LOX to provide ventilatory support |
US10136859B2 (en) | 2014-12-23 | 2018-11-27 | Michael Cutaia | System and method for outpatient management of chronic disease |
US10252020B2 (en) | 2008-10-01 | 2019-04-09 | Breathe Technologies, Inc. | Ventilator with biofeedback monitoring and control for improving patient activity and health |
WO2019163609A1 (en) * | 2018-02-21 | 2019-08-29 | 帝人ファーマ株式会社 | Server, monitor system, terminal, monitor device, and method, for monitoring oxygen concentration device |
WO2022221168A1 (en) * | 2021-04-11 | 2022-10-20 | Khurana Vikas | System for pulse cycle harmonized ventilation and the method thereof |
Families Citing this family (564)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7758503B2 (en) * | 1997-01-27 | 2010-07-20 | Lynn Lawrence A | Microprocessor system for the analysis of physiologic and financial datasets |
US9042952B2 (en) | 1997-01-27 | 2015-05-26 | Lawrence A. Lynn | System and method for automatic detection of a plurality of SPO2 time series pattern types |
US20060161071A1 (en) * | 1997-01-27 | 2006-07-20 | Lynn Lawrence A | Time series objectification system and method |
US8932227B2 (en) * | 2000-07-28 | 2015-01-13 | Lawrence A. Lynn | System and method for CO2 and oximetry integration |
US9521971B2 (en) | 1997-07-14 | 2016-12-20 | Lawrence A. Lynn | System and method for automatic detection of a plurality of SPO2 time series pattern types |
US20070191697A1 (en) * | 2006-02-10 | 2007-08-16 | Lynn Lawrence A | System and method for SPO2 instability detection and quantification |
US6371114B1 (en) * | 1998-07-24 | 2002-04-16 | Minnesota Innovative Technologies & Instruments Corporation | Control device for supplying supplemental respiratory oxygen |
US20070000494A1 (en) * | 1999-06-30 | 2007-01-04 | Banner Michael J | Ventilator monitor system and method of using same |
EP1189649B1 (en) * | 1999-06-30 | 2005-06-15 | University Of Florida Research Foundation, Inc. | Ventilator monitor system |
US20020195105A1 (en) * | 2000-01-13 | 2002-12-26 | Brent Blue | Method and apparatus for providing and controlling oxygen supply |
US6644312B2 (en) * | 2000-03-07 | 2003-11-11 | Resmed Limited | Determining suitable ventilator settings for patients with alveolar hypoventilation during sleep |
US6938619B1 (en) * | 2000-06-13 | 2005-09-06 | Scott Laboratories, Inc. | Mask free delivery of oxygen and ventilatory monitoring |
US6814073B2 (en) * | 2000-08-29 | 2004-11-09 | Resmed Limited | Respiratory apparatus with improved flow-flattening detection |
US6512938B2 (en) * | 2000-12-12 | 2003-01-28 | Nelson R. Claure | System and method for closed loop controlled inspired oxygen concentration |
IL140977A0 (en) * | 2001-01-18 | 2002-02-10 | Automed Automatic Dosage Syste | Automatically regulating oxygen flow to a patient |
US20060195041A1 (en) | 2002-05-17 | 2006-08-31 | Lynn Lawrence A | Centralized hospital monitoring system for automatically detecting upper airway instability and for preventing and aborting adverse drug reactions |
US9053222B2 (en) * | 2002-05-17 | 2015-06-09 | Lawrence A. Lynn | Patient safety processor |
US20030140924A1 (en) * | 2001-11-06 | 2003-07-31 | Aylsworth Alonzo C. | Therapeutic gas conserver and control |
US20070167853A1 (en) * | 2002-01-22 | 2007-07-19 | Melker Richard J | System and method for monitoring health using exhaled breath |
US20080200775A1 (en) | 2007-02-20 | 2008-08-21 | Lynn Lawrence A | Maneuver-based plethysmographic pulse variation detection system and method |
EP1513443B1 (en) * | 2002-06-20 | 2012-10-03 | University of Florida | Perfusion monitor and system, including specifically configured oximeter probes and covers for oximeter probes |
US6909912B2 (en) * | 2002-06-20 | 2005-06-21 | University Of Florida | Non-invasive perfusion monitor and system, specially configured oximeter probes, methods of using same, and covers for probes |
DE10230165A1 (en) * | 2002-07-04 | 2004-01-15 | Ino Therapeutics Gmbh | Method and device for the administration of carbon monoxide |
US20040129273A1 (en) * | 2002-10-03 | 2004-07-08 | Scott Laboratories, Inc. | Bite block apparatus and method for use with a sedation and analgesia system |
KR200337953Y1 (en) * | 2002-10-18 | 2004-01-07 | 마츠시타 덴끼 산교 가부시키가이샤 | Oxygen enrichment apparatus |
US20050010125A1 (en) * | 2002-11-26 | 2005-01-13 | Joy James A. | Systems and methods for respiration measurement |
US6910481B2 (en) * | 2003-03-28 | 2005-06-28 | Ric Investments, Inc. | Pressure support compliance monitoring system |
US20070084897A1 (en) | 2003-05-20 | 2007-04-19 | Shelton Frederick E Iv | Articulating surgical stapling instrument incorporating a two-piece e-beam firing mechanism |
US9060770B2 (en) | 2003-05-20 | 2015-06-23 | Ethicon Endo-Surgery, Inc. | Robotically-driven surgical instrument with E-beam driver |
DE10337138A1 (en) * | 2003-08-11 | 2005-03-17 | Freitag, Lutz, Dr. | Method and arrangement for the respiratory assistance of a patient as well as tracheal prosthesis and catheter |
CN108837255B (en) * | 2003-06-20 | 2020-12-22 | 瑞思迈私人有限公司 | Breathable gas device with humidifier |
US7135059B2 (en) * | 2003-10-07 | 2006-11-14 | Inogen, Inc. | Portable gas fractionalization system |
US20050072426A1 (en) * | 2003-10-07 | 2005-04-07 | Deane Geoffrey Frank | Portable gas fractionalization system |
US20050072423A1 (en) * | 2003-10-07 | 2005-04-07 | Deane Geoffrey Frank | Portable gas fractionalization system |
US7066985B2 (en) * | 2003-10-07 | 2006-06-27 | Inogen, Inc. | Portable gas fractionalization system |
CA2540599C (en) | 2003-10-07 | 2013-09-03 | Inogen, Inc. | Portable gas fractionalization system |
US20050217668A1 (en) * | 2003-10-24 | 2005-10-06 | Pulmonox Technologies Corporation | System and elements for managing therapeutic gas administration to a spontaneously breathing non-ventilated patient |
US7552731B2 (en) * | 2003-11-14 | 2009-06-30 | Remcore, Inc. | Remote control gas regulation system |
US7802571B2 (en) * | 2003-11-21 | 2010-09-28 | Tehrani Fleur T | Method and apparatus for controlling a ventilator |
EP2486850B1 (en) * | 2003-12-30 | 2014-09-17 | University of Florida Research Foundation, Inc. | Specially configured nasal pulse oximeter |
US7222624B2 (en) * | 2004-07-02 | 2007-05-29 | Praxair Technology, Inc. | Dual sensor oxygen therapy device |
US7013898B2 (en) | 2004-07-09 | 2006-03-21 | Praxair Technology, Inc. | Nasal pressure sensor oxygen therapy device |
US11896225B2 (en) | 2004-07-28 | 2024-02-13 | Cilag Gmbh International | Staple cartridge comprising a pan |
US8215531B2 (en) | 2004-07-28 | 2012-07-10 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument having a medical substance dispenser |
CA2577867A1 (en) * | 2004-08-27 | 2006-03-09 | Johns Hopkins University | Disposable sleep and breathing monitor |
US7455717B2 (en) * | 2004-10-25 | 2008-11-25 | Invacare Corporation | Apparatus and method of providing concentrated product gas |
US20060124128A1 (en) * | 2004-11-12 | 2006-06-15 | Deane Geoffrey F | Portable intelligent controller for therapeutic gas systems |
US20060211981A1 (en) * | 2004-12-27 | 2006-09-21 | Integrated Sensing Systems, Inc. | Medical treatment procedure and system in which bidirectional fluid flow is sensed |
DE102004063698B4 (en) * | 2004-12-28 | 2010-02-04 | Dae Systems Gmbh | Emergency oxygen system for aircraft passengers |
US20060225737A1 (en) * | 2005-04-12 | 2006-10-12 | Mr. Mario Iobbi | Device and method for automatically regulating supplemental oxygen flow-rate |
US20060249151A1 (en) * | 2005-05-03 | 2006-11-09 | China Resource Group, Inc. | Ventilator with rescuer and victim guidance |
ITRM20050217A1 (en) * | 2005-05-06 | 2006-11-07 | Ginevri S R L | PROCEDURE FOR NASAL VENTILATION AND ITS APPARATUS, IN PARTICULAR FOR NEONATAL FLOW-SYNCHRONIZED ASSISTED VENTILATION. |
ITMI20050866A1 (en) | 2005-05-13 | 2006-11-14 | Marco Ranucci | MONITORING SYSTEM FOR CARDIAC SURGERY INTERVENTIONS WITH CARDIOPOLMONARY BYPASS |
US8561611B2 (en) * | 2005-06-21 | 2013-10-22 | Ric Investments, Llc | Respiratory device measurement system |
US20070044799A1 (en) * | 2005-07-08 | 2007-03-01 | Hete Bernie F | Modular oxygen regulator system and respiratory treatment system |
US7669746B2 (en) | 2005-08-31 | 2010-03-02 | Ethicon Endo-Surgery, Inc. | Staple cartridges for forming staples having differing formed staple heights |
US10159482B2 (en) | 2005-08-31 | 2018-12-25 | Ethicon Llc | Fastener cartridge assembly comprising a fixed anvil and different staple heights |
US11246590B2 (en) | 2005-08-31 | 2022-02-15 | Cilag Gmbh International | Staple cartridge including staple drivers having different unfired heights |
US9237891B2 (en) | 2005-08-31 | 2016-01-19 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical stapling devices that produce formed staples having different lengths |
US11484312B2 (en) | 2005-08-31 | 2022-11-01 | Cilag Gmbh International | Staple cartridge comprising a staple driver arrangement |
US7934630B2 (en) | 2005-08-31 | 2011-05-03 | Ethicon Endo-Surgery, Inc. | Staple cartridges for forming staples having differing formed staple heights |
US8893717B2 (en) | 2005-09-21 | 2014-11-25 | Ino Therapeutics Llc | Systems and methods of administering a pharmaceutical gas to a patient |
US7523752B2 (en) | 2005-09-21 | 2009-04-28 | Ino Therapeutics, Llc | System and method of administering a pharmaceutical gas to a patient |
US20070077200A1 (en) * | 2005-09-30 | 2007-04-05 | Baker Clark R | Method and system for controlled maintenance of hypoxia for therapeutic or diagnostic purposes |
US7942824B1 (en) * | 2005-11-04 | 2011-05-17 | Cleveland Medical Devices Inc. | Integrated sleep diagnostic and therapeutic system and method |
US8545416B1 (en) * | 2005-11-04 | 2013-10-01 | Cleveland Medical Devices Inc. | Integrated diagnostic and therapeutic system and method for improving treatment of subject with complex and central sleep apnea |
US20070106317A1 (en) | 2005-11-09 | 2007-05-10 | Shelton Frederick E Iv | Hydraulically and electrically actuated articulation joints for surgical instruments |
US7686870B1 (en) | 2005-12-29 | 2010-03-30 | Inogen, Inc. | Expandable product rate portable gas fractionalization system |
NZ552009A (en) * | 2006-01-24 | 2007-10-26 | Devx Tech Ip Ltd | Hypoxic training apparatus with gas supply from primary, secondary and tertiary sources |
US8820603B2 (en) | 2006-01-31 | 2014-09-02 | Ethicon Endo-Surgery, Inc. | Accessing data stored in a memory of a surgical instrument |
US7753904B2 (en) | 2006-01-31 | 2010-07-13 | Ethicon Endo-Surgery, Inc. | Endoscopic surgical instrument with a handle that can articulate with respect to the shaft |
US7845537B2 (en) | 2006-01-31 | 2010-12-07 | Ethicon Endo-Surgery, Inc. | Surgical instrument having recording capabilities |
US8708213B2 (en) | 2006-01-31 | 2014-04-29 | Ethicon Endo-Surgery, Inc. | Surgical instrument having a feedback system |
US11793518B2 (en) | 2006-01-31 | 2023-10-24 | Cilag Gmbh International | Powered surgical instruments with firing system lockout arrangements |
US8186555B2 (en) | 2006-01-31 | 2012-05-29 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting and fastening instrument with mechanical closure system |
US20110295295A1 (en) | 2006-01-31 | 2011-12-01 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical instrument having recording capabilities |
US20110024477A1 (en) | 2009-02-06 | 2011-02-03 | Hall Steven G | Driven Surgical Stapler Improvements |
US20120292367A1 (en) | 2006-01-31 | 2012-11-22 | Ethicon Endo-Surgery, Inc. | Robotically-controlled end effector |
US11224427B2 (en) | 2006-01-31 | 2022-01-18 | Cilag Gmbh International | Surgical stapling system including a console and retraction assembly |
US11278279B2 (en) | 2006-01-31 | 2022-03-22 | Cilag Gmbh International | Surgical instrument assembly |
US7668579B2 (en) | 2006-02-10 | 2010-02-23 | Lynn Lawrence A | System and method for the detection of physiologic response to stimulation |
GB2436151B (en) * | 2006-03-15 | 2009-09-30 | Honeywell Normalair Garrett | Method of controlling a gas separating apparatus |
US8992422B2 (en) | 2006-03-23 | 2015-03-31 | Ethicon Endo-Surgery, Inc. | Robotically-controlled endoscopic accessory channel |
US20070283958A1 (en) * | 2006-05-23 | 2007-12-13 | Ray Naghavi | Positive airway pressure device |
US8322455B2 (en) | 2006-06-27 | 2012-12-04 | Ethicon Endo-Surgery, Inc. | Manually driven surgical cutting and fastening instrument |
US20080066752A1 (en) * | 2006-09-20 | 2008-03-20 | Nellcor Puritan Bennett Inc. | Method and system for circulatory delay compensation in closed-loop control of a medical device |
US10568652B2 (en) | 2006-09-29 | 2020-02-25 | Ethicon Llc | Surgical staples having attached drivers of different heights and stapling instruments for deploying the same |
US8728059B2 (en) | 2006-09-29 | 2014-05-20 | Covidien Lp | System and method for assuring validity of monitoring parameter in combination with a therapeutic device |
US7506791B2 (en) | 2006-09-29 | 2009-03-24 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument with mechanical mechanism for limiting maximum tissue compression |
US8652120B2 (en) | 2007-01-10 | 2014-02-18 | Ethicon Endo-Surgery, Inc. | Surgical instrument with wireless communication between control unit and sensor transponders |
US8684253B2 (en) | 2007-01-10 | 2014-04-01 | Ethicon Endo-Surgery, Inc. | Surgical instrument with wireless communication between a control unit of a robotic system and remote sensor |
US11291441B2 (en) | 2007-01-10 | 2022-04-05 | Cilag Gmbh International | Surgical instrument with wireless communication between control unit and remote sensor |
US11039836B2 (en) | 2007-01-11 | 2021-06-22 | Cilag Gmbh International | Staple cartridge for use with a surgical stapling instrument |
US8701958B2 (en) | 2007-01-11 | 2014-04-22 | Ethicon Endo-Surgery, Inc. | Curved end effector for a surgical stapling device |
US20080200819A1 (en) * | 2007-02-20 | 2008-08-21 | Lynn Lawrence A | Orthostasis detection system and method |
US20080202521A1 (en) * | 2007-02-23 | 2008-08-28 | General Electric Company | Setting mandatory mechanical ventilation parameters based on patient physiology |
US7669747B2 (en) | 2007-03-15 | 2010-03-02 | Ethicon Endo-Surgery, Inc. | Washer for use with a surgical stapling instrument |
US20080230062A1 (en) * | 2007-03-23 | 2008-09-25 | General Electric Company | Setting expiratory time in mandatory mechanical ventilation based on a deviation from a stable condition of exhaled gas volumes |
US8893946B2 (en) | 2007-03-28 | 2014-11-25 | Ethicon Endo-Surgery, Inc. | Laparoscopic tissue thickness and clamp load measuring devices |
US8695593B2 (en) * | 2007-03-31 | 2014-04-15 | Fleur T. Tehrani | Weaning and decision support system for mechanical ventilation |
CN103657334B (en) | 2007-04-20 | 2016-03-09 | 英瓦卡尔公司 | Product gas inspissator and correlation technique thereof |
US11564682B2 (en) | 2007-06-04 | 2023-01-31 | Cilag Gmbh International | Surgical stapler device |
US8931682B2 (en) | 2007-06-04 | 2015-01-13 | Ethicon Endo-Surgery, Inc. | Robotically-controlled shaft based rotary drive systems for surgical instruments |
US7753245B2 (en) | 2007-06-22 | 2010-07-13 | Ethicon Endo-Surgery, Inc. | Surgical stapling instruments |
US11849941B2 (en) | 2007-06-29 | 2023-12-26 | Cilag Gmbh International | Staple cartridge having staple cavities extending at a transverse angle relative to a longitudinal cartridge axis |
US20090065007A1 (en) | 2007-09-06 | 2009-03-12 | Wilkinson William R | Oxygen concentrator apparatus and method |
US20090133695A1 (en) * | 2007-11-27 | 2009-05-28 | Rao Chamkurkishtiah P | Mechanical ventilator system |
US20090163774A1 (en) * | 2007-12-20 | 2009-06-25 | Sudeesh Thatha | Managment and Diagnostic System for Patient Monitoring and Symptom Analysis |
US9179912B2 (en) | 2008-02-14 | 2015-11-10 | Ethicon Endo-Surgery, Inc. | Robotically-controlled motorized surgical cutting and fastening instrument |
US7866527B2 (en) | 2008-02-14 | 2011-01-11 | Ethicon Endo-Surgery, Inc. | Surgical stapling apparatus with interlockable firing system |
JP5410110B2 (en) | 2008-02-14 | 2014-02-05 | エシコン・エンド−サージェリィ・インコーポレイテッド | Surgical cutting / fixing instrument with RF electrode |
US7819298B2 (en) | 2008-02-14 | 2010-10-26 | Ethicon Endo-Surgery, Inc. | Surgical stapling apparatus with control features operable with one hand |
US8758391B2 (en) | 2008-02-14 | 2014-06-24 | Ethicon Endo-Surgery, Inc. | Interchangeable tools for surgical instruments |
US8636736B2 (en) | 2008-02-14 | 2014-01-28 | Ethicon Endo-Surgery, Inc. | Motorized surgical cutting and fastening instrument |
US8573465B2 (en) | 2008-02-14 | 2013-11-05 | Ethicon Endo-Surgery, Inc. | Robotically-controlled surgical end effector system with rotary actuated closure systems |
US11272927B2 (en) | 2008-02-15 | 2022-03-15 | Cilag Gmbh International | Layer arrangements for surgical staple cartridges |
US20130153641A1 (en) | 2008-02-15 | 2013-06-20 | Ethicon Endo-Surgery, Inc. | Releasable layer of material and surgical end effector having the same |
US7722698B2 (en) | 2008-02-21 | 2010-05-25 | Delphi Technologies, Inc. | Method of determining the purity of oxygen present in an oxygen-enriched gas produced from an oxygen delivery system |
US20090211443A1 (en) * | 2008-02-21 | 2009-08-27 | Youngblood James H | Self-serviceable filter for an oxygen generating device |
US8075676B2 (en) | 2008-02-22 | 2011-12-13 | Oxus America, Inc. | Damping apparatus for scroll compressors for oxygen-generating systems |
US20090214393A1 (en) * | 2008-02-22 | 2009-08-27 | Chekal Michael P | Method of generating an oxygen-enriched gas for a user |
US8272379B2 (en) * | 2008-03-31 | 2012-09-25 | Nellcor Puritan Bennett, Llc | Leak-compensated flow triggering and cycling in medical ventilators |
US8267085B2 (en) * | 2009-03-20 | 2012-09-18 | Nellcor Puritan Bennett Llc | Leak-compensated proportional assist ventilation |
US8746248B2 (en) | 2008-03-31 | 2014-06-10 | Covidien Lp | Determination of patient circuit disconnect in leak-compensated ventilatory support |
US10207069B2 (en) | 2008-03-31 | 2019-02-19 | Covidien Lp | System and method for determining ventilator leakage during stable periods within a breath |
WO2009125300A2 (en) | 2008-04-07 | 2009-10-15 | Uti Limited Partnership | Oxygenation procedures for newborns and devices for use therein |
US9120050B2 (en) | 2008-04-21 | 2015-09-01 | Invacare Corporation | Product gas concentrator utilizing vacuum swing adsorption and method associated therewith |
US8457706B2 (en) * | 2008-05-16 | 2013-06-04 | Covidien Lp | Estimation of a physiological parameter using a neural network |
EP2320791B1 (en) | 2008-06-06 | 2016-08-31 | Covidien LP | Systems for ventilation in proportion to patient effort |
TW201000159A (en) * | 2008-06-27 | 2010-01-01 | chang-an Zhou | Expandable type gas delivering system and gas delivering method thereof |
US8862194B2 (en) * | 2008-06-30 | 2014-10-14 | Covidien Lp | Method for improved oxygen saturation estimation in the presence of noise |
US20090320836A1 (en) * | 2008-06-30 | 2009-12-31 | Baker Jr Clark R | Method For Regulating Treatment Based On A Medical Device Under Closed-Loop Physiologic Control |
US8186346B2 (en) | 2008-07-23 | 2012-05-29 | Chart Sequal Technologies Inc. | Self-automated titration system and method |
US8551006B2 (en) * | 2008-09-17 | 2013-10-08 | Covidien Lp | Method for determining hemodynamic effects |
US11648005B2 (en) | 2008-09-23 | 2023-05-16 | Cilag Gmbh International | Robotically-controlled motorized surgical instrument with an end effector |
US9386983B2 (en) | 2008-09-23 | 2016-07-12 | Ethicon Endo-Surgery, Llc | Robotically-controlled motorized surgical instrument |
US8210411B2 (en) | 2008-09-23 | 2012-07-03 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting instrument |
US9005230B2 (en) | 2008-09-23 | 2015-04-14 | Ethicon Endo-Surgery, Inc. | Motorized surgical instrument |
US20100071696A1 (en) * | 2008-09-25 | 2010-03-25 | Nellcor Puritan Bennett Llc | Model-predictive online identification of patient respiratory effort dynamics in medical ventilators |
US8302602B2 (en) | 2008-09-30 | 2012-11-06 | Nellcor Puritan Bennett Llc | Breathing assistance system with multiple pressure sensors |
NL1036012C (en) * | 2008-10-03 | 2010-04-06 | Stephan Arend Hulsbergen | MONITORING SYSTEM, RING FITTED WITH SUCH A SYSTEM, AND A SENSOR AND A PROCESSING UNIT AS PART OF THIS SYSTEM. |
US8608045B2 (en) | 2008-10-10 | 2013-12-17 | Ethicon Endo-Sugery, Inc. | Powered surgical cutting and stapling apparatus with manually retractable firing system |
DE102009013396B3 (en) * | 2009-03-16 | 2010-08-05 | Dräger Medical AG & Co. KG | Apparatus and method for controlling the oxygen dosage of a ventilator |
US8082312B2 (en) * | 2008-12-12 | 2011-12-20 | Event Medical, Inc. | System and method for communicating over a network with a medical device |
US8517239B2 (en) | 2009-02-05 | 2013-08-27 | Ethicon Endo-Surgery, Inc. | Surgical stapling instrument comprising a magnetic element driver |
US8444036B2 (en) | 2009-02-06 | 2013-05-21 | Ethicon Endo-Surgery, Inc. | Motor driven surgical fastener device with mechanisms for adjusting a tissue gap within the end effector |
EP2393430A1 (en) | 2009-02-06 | 2011-12-14 | Ethicon Endo-Surgery, Inc. | Driven surgical stapler improvements |
US8434479B2 (en) * | 2009-02-27 | 2013-05-07 | Covidien Lp | Flow rate compensation for transient thermal response of hot-wire anemometers |
US8424521B2 (en) | 2009-02-27 | 2013-04-23 | Covidien Lp | Leak-compensated respiratory mechanics estimation in medical ventilators |
US8418691B2 (en) * | 2009-03-20 | 2013-04-16 | Covidien Lp | Leak-compensated pressure regulated volume control ventilation |
US9364623B2 (en) * | 2009-07-15 | 2016-06-14 | UNIVERSITé LAVAL | Method and device for administering oxygen to a patient and monitoring the patient |
US8596270B2 (en) * | 2009-08-20 | 2013-12-03 | Covidien Lp | Systems and methods for controlling a ventilator |
US8789529B2 (en) | 2009-08-20 | 2014-07-29 | Covidien Lp | Method for ventilation |
CA2774902C (en) | 2009-09-03 | 2017-01-03 | Breathe Technologies, Inc. | Methods, systems and devices for non-invasive ventilation including a non-sealing ventilation interface with an entrainment port and/or pressure feature |
US8851354B2 (en) | 2009-12-24 | 2014-10-07 | Ethicon Endo-Surgery, Inc. | Surgical cutting instrument that analyzes tissue thickness |
US8220688B2 (en) | 2009-12-24 | 2012-07-17 | Ethicon Endo-Surgery, Inc. | Motor-driven surgical cutting instrument with electric actuator directional control assembly |
JP5571697B2 (en) * | 2010-01-12 | 2014-08-13 | 帝人ファーマ株式会社 | Oxygen concentrator |
US8171094B2 (en) * | 2010-01-19 | 2012-05-01 | Event Medical, Inc. | System and method for communicating over a network with a medical device |
US9974918B2 (en) * | 2010-04-07 | 2018-05-22 | Caire Inc. | Portable oxygen delivery device |
US10821243B2 (en) | 2010-04-13 | 2020-11-03 | Advanced Interactive Response Systems, LLC | Gas supply warning and communication system |
US11511062B2 (en) | 2010-04-13 | 2022-11-29 | Advanced Interactive Response Systems LLC | Gas supply warning and communication system |
US8653979B2 (en) * | 2010-04-13 | 2014-02-18 | Valerie A. Obenchain | Gas flow and pressure error alarm |
US8676285B2 (en) | 2010-07-28 | 2014-03-18 | Covidien Lp | Methods for validating patient identity |
US8783543B2 (en) | 2010-07-30 | 2014-07-22 | Ethicon Endo-Surgery, Inc. | Tissue acquisition arrangements and methods for surgical stapling devices |
EP2605817A4 (en) * | 2010-08-10 | 2014-09-17 | Univ California | Automated fluid delivery system and method |
US8603228B2 (en) | 2010-09-07 | 2013-12-10 | Inova Labs, Inc. | Power management systems and methods for use in an oxygen concentrator |
US8616207B2 (en) | 2010-09-07 | 2013-12-31 | Inova Labs, Inc. | Oxygen concentrator heat management system and method |
US8554298B2 (en) | 2010-09-21 | 2013-10-08 | Cividien LP | Medical ventilator with integrated oximeter data |
US11298125B2 (en) | 2010-09-30 | 2022-04-12 | Cilag Gmbh International | Tissue stapler having a thickness compensator |
US8746535B2 (en) | 2010-09-30 | 2014-06-10 | Ethicon Endo-Surgery, Inc. | Tissue thickness compensator comprising detachable portions |
US9517063B2 (en) | 2012-03-28 | 2016-12-13 | Ethicon Endo-Surgery, Llc | Movable member for use with a tissue thickness compensator |
US11812965B2 (en) | 2010-09-30 | 2023-11-14 | Cilag Gmbh International | Layer of material for a surgical end effector |
US9364233B2 (en) | 2010-09-30 | 2016-06-14 | Ethicon Endo-Surgery, Llc | Tissue thickness compensators for circular surgical staplers |
US9386988B2 (en) | 2010-09-30 | 2016-07-12 | Ethicon End-Surgery, LLC | Retainer assembly including a tissue thickness compensator |
US10945731B2 (en) | 2010-09-30 | 2021-03-16 | Ethicon Llc | Tissue thickness compensator comprising controlled release and expansion |
US11849952B2 (en) | 2010-09-30 | 2023-12-26 | Cilag Gmbh International | Staple cartridge comprising staples positioned within a compressible portion thereof |
US9839420B2 (en) | 2010-09-30 | 2017-12-12 | Ethicon Llc | Tissue thickness compensator comprising at least one medicament |
US9629814B2 (en) | 2010-09-30 | 2017-04-25 | Ethicon Endo-Surgery, Llc | Tissue thickness compensator configured to redistribute compressive forces |
US9566061B2 (en) | 2010-09-30 | 2017-02-14 | Ethicon Endo-Surgery, Llc | Fastener cartridge comprising a releasably attached tissue thickness compensator |
US8695866B2 (en) | 2010-10-01 | 2014-04-15 | Ethicon Endo-Surgery, Inc. | Surgical instrument having a power control circuit |
US8783250B2 (en) | 2011-02-27 | 2014-07-22 | Covidien Lp | Methods and systems for transitory ventilation support |
US20140007870A1 (en) * | 2011-03-24 | 2014-01-09 | Oskar Frånberg | Device and method for supplying and dosing gas to a breathing person |
US8714154B2 (en) | 2011-03-30 | 2014-05-06 | Covidien Lp | Systems and methods for automatic adjustment of ventilator settings |
AU2012250197B2 (en) | 2011-04-29 | 2017-08-10 | Ethicon Endo-Surgery, Inc. | Staple cartridge comprising staples positioned within a compressible portion thereof |
US9072535B2 (en) | 2011-05-27 | 2015-07-07 | Ethicon Endo-Surgery, Inc. | Surgical stapling instruments with rotatable staple deployment arrangements |
US11207064B2 (en) | 2011-05-27 | 2021-12-28 | Cilag Gmbh International | Automated end effector component reloading system for use with a robotic system |
US20140202455A1 (en) * | 2011-08-25 | 2014-07-24 | Koninklijke Philips N.V. | Method and apparatus for controlling a ventilation therapy device |
US9089657B2 (en) | 2011-10-31 | 2015-07-28 | Covidien Lp | Methods and systems for gating user initiated increases in oxygen concentration during ventilation |
US20130201316A1 (en) | 2012-01-09 | 2013-08-08 | May Patents Ltd. | System and method for server based control |
US9044230B2 (en) | 2012-02-13 | 2015-06-02 | Ethicon Endo-Surgery, Inc. | Surgical cutting and fastening instrument with apparatus for determining cartridge and firing motion status |
WO2013134645A1 (en) | 2012-03-09 | 2013-09-12 | Invacare Corporation | System and method for concentrating gas by adsorption |
US9266053B2 (en) | 2012-06-18 | 2016-02-23 | Invacare Corporation | System and method for concentrating gas |
US9067174B2 (en) | 2012-03-09 | 2015-06-30 | Invacare Corporation | System and method for concentrating gas |
CN104411317A (en) | 2012-03-15 | 2015-03-11 | Ino治疗有限责任公司 | Methods of administering high concentrations of nitric oxide |
MX358135B (en) | 2012-03-28 | 2018-08-06 | Ethicon Endo Surgery Inc | Tissue thickness compensator comprising a plurality of layers. |
RU2639857C2 (en) | 2012-03-28 | 2017-12-22 | Этикон Эндо-Серджери, Инк. | Tissue thickness compensator containing capsule for medium with low pressure |
RU2644272C2 (en) | 2012-03-28 | 2018-02-08 | Этикон Эндо-Серджери, Инк. | Limitation node with tissue thickness compensator |
US9993604B2 (en) | 2012-04-27 | 2018-06-12 | Covidien Lp | Methods and systems for an optimized proportional assist ventilation |
US9101358B2 (en) | 2012-06-15 | 2015-08-11 | Ethicon Endo-Surgery, Inc. | Articulatable surgical instrument comprising a firing drive |
US9289256B2 (en) | 2012-06-28 | 2016-03-22 | Ethicon Endo-Surgery, Llc | Surgical end effectors having angled tissue-contacting surfaces |
BR112014032776B1 (en) | 2012-06-28 | 2021-09-08 | Ethicon Endo-Surgery, Inc | SURGICAL INSTRUMENT SYSTEM AND SURGICAL KIT FOR USE WITH A SURGICAL INSTRUMENT SYSTEM |
EP2866686A1 (en) | 2012-06-28 | 2015-05-06 | Ethicon Endo-Surgery, Inc. | Empty clip cartridge lockout |
US20140001231A1 (en) | 2012-06-28 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Firing system lockout arrangements for surgical instruments |
US20140005718A1 (en) | 2012-06-28 | 2014-01-02 | Ethicon Endo-Surgery, Inc. | Multi-functional powered surgical device with external dissection features |
US9649111B2 (en) | 2012-06-28 | 2017-05-16 | Ethicon Endo-Surgery, Llc | Replaceable clip cartridge for a clip applier |
US9226751B2 (en) | 2012-06-28 | 2016-01-05 | Ethicon Endo-Surgery, Inc. | Surgical instrument system including replaceable end effectors |
US11202631B2 (en) | 2012-06-28 | 2021-12-21 | Cilag Gmbh International | Stapling assembly comprising a firing lockout |
US10362967B2 (en) | 2012-07-09 | 2019-07-30 | Covidien Lp | Systems and methods for missed breath detection and indication |
US9138557B2 (en) | 2012-10-12 | 2015-09-22 | Inova Labs, Inc. | Dual oxygen concentrator systems and methods |
NZ707064A (en) | 2012-10-12 | 2017-11-24 | Inova Labs Inc | Method and systems for the delivery of oxygen enriched gas |
EP2906280B1 (en) | 2012-10-12 | 2018-09-26 | Inova Labs, Inc. | Oxygen concentrator systems and methods |
US9375542B2 (en) | 2012-11-08 | 2016-06-28 | Covidien Lp | Systems and methods for monitoring, managing, and/or preventing fatigue during ventilation |
GB2508897B (en) * | 2012-12-14 | 2016-02-10 | Bahram Kandar | Oxygen flow controller for medical use |
CN104955511B (en) * | 2013-01-29 | 2017-08-11 | 皇家飞利浦有限公司 | The control of neonate's oxygen supply |
RU2672520C2 (en) | 2013-03-01 | 2018-11-15 | Этикон Эндо-Серджери, Инк. | Hingedly turnable surgical instruments with conducting ways for signal transfer |
RU2669463C2 (en) | 2013-03-01 | 2018-10-11 | Этикон Эндо-Серджери, Инк. | Surgical instrument with soft stop |
US9629629B2 (en) | 2013-03-14 | 2017-04-25 | Ethicon Endo-Surgey, LLC | Control systems for surgical instruments |
US9332987B2 (en) | 2013-03-14 | 2016-05-10 | Ethicon Endo-Surgery, Llc | Control arrangements for a drive member of a surgical instrument |
US9867612B2 (en) | 2013-04-16 | 2018-01-16 | Ethicon Llc | Powered surgical stapler |
BR112015026109B1 (en) | 2013-04-16 | 2022-02-22 | Ethicon Endo-Surgery, Inc | surgical instrument |
US9775609B2 (en) | 2013-08-23 | 2017-10-03 | Ethicon Llc | Tamper proof circuit for surgical instrument battery pack |
MX369362B (en) | 2013-08-23 | 2019-11-06 | Ethicon Endo Surgery Llc | Firing member retraction devices for powered surgical instruments. |
US9675771B2 (en) | 2013-10-18 | 2017-06-13 | Covidien Lp | Methods and systems for leak estimation |
EP2893948A1 (en) | 2014-01-10 | 2015-07-15 | Fundació Institut d'Investigació Biomèdica de Bellvitge (IDIBELL) | Methods and systems for providing oxygen to a patient |
US9962161B2 (en) | 2014-02-12 | 2018-05-08 | Ethicon Llc | Deliverable surgical instrument |
US9440179B2 (en) | 2014-02-14 | 2016-09-13 | InovaLabs, LLC | Oxygen concentrator pump systems and methods |
JP6462004B2 (en) | 2014-02-24 | 2019-01-30 | エシコン エルエルシー | Fastening system with launcher lockout |
US20150272557A1 (en) | 2014-03-26 | 2015-10-01 | Ethicon Endo-Surgery, Inc. | Modular surgical instrument system |
BR112016021943B1 (en) | 2014-03-26 | 2022-06-14 | Ethicon Endo-Surgery, Llc | SURGICAL INSTRUMENT FOR USE BY AN OPERATOR IN A SURGICAL PROCEDURE |
US9826977B2 (en) | 2014-03-26 | 2017-11-28 | Ethicon Llc | Sterilization verification circuit |
US10028761B2 (en) | 2014-03-26 | 2018-07-24 | Ethicon Llc | Feedback algorithms for manual bailout systems for surgical instruments |
JP6532889B2 (en) | 2014-04-16 | 2019-06-19 | エシコン エルエルシーEthicon LLC | Fastener cartridge assembly and staple holder cover arrangement |
US10206677B2 (en) | 2014-09-26 | 2019-02-19 | Ethicon Llc | Surgical staple and driver arrangements for staple cartridges |
JP6612256B2 (en) | 2014-04-16 | 2019-11-27 | エシコン エルエルシー | Fastener cartridge with non-uniform fastener |
US9844369B2 (en) | 2014-04-16 | 2017-12-19 | Ethicon Llc | Surgical end effectors with firing element monitoring arrangements |
US20150297223A1 (en) | 2014-04-16 | 2015-10-22 | Ethicon Endo-Surgery, Inc. | Fastener cartridges including extensions having different configurations |
CN106456176B (en) | 2014-04-16 | 2019-06-28 | 伊西康内外科有限责任公司 | Fastener cartridge including the extension with various configuration |
DE102014107980A1 (en) * | 2014-06-05 | 2015-12-17 | Hamilton Medical Ag | Ventilation system with mechanical ventilation and extracorporeal blood gas exchange |
US9808591B2 (en) | 2014-08-15 | 2017-11-07 | Covidien Lp | Methods and systems for breath delivery synchronization |
BR112017004361B1 (en) | 2014-09-05 | 2023-04-11 | Ethicon Llc | ELECTRONIC SYSTEM FOR A SURGICAL INSTRUMENT |
US20160066913A1 (en) | 2014-09-05 | 2016-03-10 | Ethicon Endo-Surgery, Inc. | Local display of tissue parameter stabilization |
US11311294B2 (en) | 2014-09-05 | 2022-04-26 | Cilag Gmbh International | Powered medical device including measurement of closure state of jaws |
US10105142B2 (en) | 2014-09-18 | 2018-10-23 | Ethicon Llc | Surgical stapler with plurality of cutting elements |
JP6648119B2 (en) | 2014-09-26 | 2020-02-14 | エシコン エルエルシーEthicon LLC | Surgical stapling buttress and accessory materials |
US11523821B2 (en) | 2014-09-26 | 2022-12-13 | Cilag Gmbh International | Method for creating a flexible staple line |
US10076325B2 (en) | 2014-10-13 | 2018-09-18 | Ethicon Llc | Surgical stapling apparatus comprising a tissue stop |
US9924944B2 (en) | 2014-10-16 | 2018-03-27 | Ethicon Llc | Staple cartridge comprising an adjunct material |
US9950129B2 (en) | 2014-10-27 | 2018-04-24 | Covidien Lp | Ventilation triggering using change-point detection |
US10517594B2 (en) | 2014-10-29 | 2019-12-31 | Ethicon Llc | Cartridge assemblies for surgical staplers |
US11141153B2 (en) | 2014-10-29 | 2021-10-12 | Cilag Gmbh International | Staple cartridges comprising driver arrangements |
US9844376B2 (en) | 2014-11-06 | 2017-12-19 | Ethicon Llc | Staple cartridge comprising a releasable adjunct material |
US20170304576A1 (en) * | 2014-11-19 | 2017-10-26 | Koninklijke Philips N.V. | Strap member for a patient interface |
US10736636B2 (en) | 2014-12-10 | 2020-08-11 | Ethicon Llc | Articulatable surgical instrument system |
US9987000B2 (en) | 2014-12-18 | 2018-06-05 | Ethicon Llc | Surgical instrument assembly comprising a flexible articulation system |
US9844374B2 (en) | 2014-12-18 | 2017-12-19 | Ethicon Llc | Surgical instrument systems comprising an articulatable end effector and means for adjusting the firing stroke of a firing member |
US10004501B2 (en) | 2014-12-18 | 2018-06-26 | Ethicon Llc | Surgical instruments with improved closure arrangements |
US9844375B2 (en) | 2014-12-18 | 2017-12-19 | Ethicon Llc | Drive arrangements for articulatable surgical instruments |
US10085748B2 (en) | 2014-12-18 | 2018-10-02 | Ethicon Llc | Locking arrangements for detachable shaft assemblies with articulatable surgical end effectors |
RU2703684C2 (en) | 2014-12-18 | 2019-10-21 | ЭТИКОН ЭНДО-СЕРДЖЕРИ, ЭлЭлСи | Surgical instrument with anvil which is selectively movable relative to staple cartridge around discrete fixed axis |
US10188385B2 (en) | 2014-12-18 | 2019-01-29 | Ethicon Llc | Surgical instrument system comprising lockable systems |
US10786645B2 (en) * | 2014-12-30 | 2020-09-29 | Koninklijke Philips N.V. | Capnometry system with supplemental oxygen detection and method of operation thereof |
US10007238B1 (en) | 2015-01-22 | 2018-06-26 | John C. Taube | Oxygen mixing and delivery |
US20180126110A1 (en) * | 2015-02-18 | 2018-05-10 | Fisher & Paykel Healthcare Limited | Flow therapy system |
US11154301B2 (en) | 2015-02-27 | 2021-10-26 | Cilag Gmbh International | Modular stapling assembly |
US20160249910A1 (en) | 2015-02-27 | 2016-09-01 | Ethicon Endo-Surgery, Llc | Surgical charging system that charges and/or conditions one or more batteries |
US10180463B2 (en) | 2015-02-27 | 2019-01-15 | Ethicon Llc | Surgical apparatus configured to assess whether a performance parameter of the surgical apparatus is within an acceptable performance band |
US10687806B2 (en) | 2015-03-06 | 2020-06-23 | Ethicon Llc | Adaptive tissue compression techniques to adjust closure rates for multiple tissue types |
US10052044B2 (en) | 2015-03-06 | 2018-08-21 | Ethicon Llc | Time dependent evaluation of sensor data to determine stability, creep, and viscoelastic elements of measures |
US10245033B2 (en) | 2015-03-06 | 2019-04-02 | Ethicon Llc | Surgical instrument comprising a lockable battery housing |
US9924961B2 (en) | 2015-03-06 | 2018-03-27 | Ethicon Endo-Surgery, Llc | Interactive feedback system for powered surgical instruments |
US9808246B2 (en) | 2015-03-06 | 2017-11-07 | Ethicon Endo-Surgery, Llc | Method of operating a powered surgical instrument |
US9993248B2 (en) | 2015-03-06 | 2018-06-12 | Ethicon Endo-Surgery, Llc | Smart sensors with local signal processing |
US9901342B2 (en) | 2015-03-06 | 2018-02-27 | Ethicon Endo-Surgery, Llc | Signal and power communication system positioned on a rotatable shaft |
US10617412B2 (en) | 2015-03-06 | 2020-04-14 | Ethicon Llc | System for detecting the mis-insertion of a staple cartridge into a surgical stapler |
JP2020121162A (en) | 2015-03-06 | 2020-08-13 | エシコン エルエルシーEthicon LLC | Time dependent evaluation of sensor data to determine stability element, creep element and viscoelastic element of measurement |
US10441279B2 (en) | 2015-03-06 | 2019-10-15 | Ethicon Llc | Multiple level thresholds to modify operation of powered surgical instruments |
ES2584915A1 (en) * | 2015-03-30 | 2016-09-30 | Universidad De Cádiz | Automatic flow dosing device for oxygen therapy equipment (Machine-translation by Google Translate, not legally binding) |
US10433844B2 (en) | 2015-03-31 | 2019-10-08 | Ethicon Llc | Surgical instrument with selectively disengageable threaded drive systems |
CA2980520A1 (en) | 2015-03-31 | 2016-10-06 | Fisher & Paykel Healthcare Limited | Methods and apparatus for high gas flow |
US20170007789A1 (en) * | 2015-07-09 | 2017-01-12 | Chang-An Chou | Extendable air delivery system and air delivery method |
US10835249B2 (en) | 2015-08-17 | 2020-11-17 | Ethicon Llc | Implantable layers for a surgical instrument |
US10105139B2 (en) | 2015-09-23 | 2018-10-23 | Ethicon Llc | Surgical stapler having downstream current-based motor control |
US10327769B2 (en) | 2015-09-23 | 2019-06-25 | Ethicon Llc | Surgical stapler having motor control based on a drive system component |
US10363036B2 (en) | 2015-09-23 | 2019-07-30 | Ethicon Llc | Surgical stapler having force-based motor control |
US10238386B2 (en) | 2015-09-23 | 2019-03-26 | Ethicon Llc | Surgical stapler having motor control based on an electrical parameter related to a motor current |
US10299878B2 (en) | 2015-09-25 | 2019-05-28 | Ethicon Llc | Implantable adjunct systems for determining adjunct skew |
US10271849B2 (en) | 2015-09-30 | 2019-04-30 | Ethicon Llc | Woven constructs with interlocked standing fibers |
US10980539B2 (en) | 2015-09-30 | 2021-04-20 | Ethicon Llc | Implantable adjunct comprising bonded layers |
US11890015B2 (en) | 2015-09-30 | 2024-02-06 | Cilag Gmbh International | Compressible adjunct with crossing spacer fibers |
US10603039B2 (en) | 2015-09-30 | 2020-03-31 | Ethicon Llc | Progressively releasable implantable adjunct for use with a surgical stapling instrument |
EP3359237A4 (en) * | 2015-10-05 | 2019-06-12 | Université Laval | Method for delivery of breathing gas to a patient and system for performing same |
AU2016354671B2 (en) * | 2015-11-10 | 2022-01-06 | University Of Tasmania | Method, apparatus and system for automatically controlling inspired oxygen delivery |
WO2017106636A1 (en) * | 2015-12-18 | 2017-06-22 | Inova Labs, Inc. | Use of an oxygen concentrator for cpap therapy |
US10368865B2 (en) | 2015-12-30 | 2019-08-06 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US10292704B2 (en) | 2015-12-30 | 2019-05-21 | Ethicon Llc | Mechanisms for compensating for battery pack failure in powered surgical instruments |
US10265068B2 (en) | 2015-12-30 | 2019-04-23 | Ethicon Llc | Surgical instruments with separable motors and motor control circuits |
US10433837B2 (en) | 2016-02-09 | 2019-10-08 | Ethicon Llc | Surgical instruments with multiple link articulation arrangements |
US11213293B2 (en) | 2016-02-09 | 2022-01-04 | Cilag Gmbh International | Articulatable surgical instruments with single articulation link arrangements |
BR112018016098B1 (en) | 2016-02-09 | 2023-02-23 | Ethicon Llc | SURGICAL INSTRUMENT |
US11224426B2 (en) | 2016-02-12 | 2022-01-18 | Cilag Gmbh International | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US10448948B2 (en) | 2016-02-12 | 2019-10-22 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
US10258331B2 (en) | 2016-02-12 | 2019-04-16 | Ethicon Llc | Mechanisms for compensating for drivetrain failure in powered surgical instruments |
WO2017165749A1 (en) | 2016-03-25 | 2017-09-28 | Separation Design Group Llc | Positive airway pressure system with integrated oxygen |
US10314582B2 (en) | 2016-04-01 | 2019-06-11 | Ethicon Llc | Surgical instrument comprising a shifting mechanism |
US10617413B2 (en) | 2016-04-01 | 2020-04-14 | Ethicon Llc | Closure system arrangements for surgical cutting and stapling devices with separate and distinct firing shafts |
US10335145B2 (en) | 2016-04-15 | 2019-07-02 | Ethicon Llc | Modular surgical instrument with configurable operating mode |
US10492783B2 (en) | 2016-04-15 | 2019-12-03 | Ethicon, Llc | Surgical instrument with improved stop/start control during a firing motion |
US10405859B2 (en) | 2016-04-15 | 2019-09-10 | Ethicon Llc | Surgical instrument with adjustable stop/start control during a firing motion |
US11179150B2 (en) | 2016-04-15 | 2021-11-23 | Cilag Gmbh International | Systems and methods for controlling a surgical stapling and cutting instrument |
US10456137B2 (en) | 2016-04-15 | 2019-10-29 | Ethicon Llc | Staple formation detection mechanisms |
US10357247B2 (en) | 2016-04-15 | 2019-07-23 | Ethicon Llc | Surgical instrument with multiple program responses during a firing motion |
US10828028B2 (en) | 2016-04-15 | 2020-11-10 | Ethicon Llc | Surgical instrument with multiple program responses during a firing motion |
US10426467B2 (en) | 2016-04-15 | 2019-10-01 | Ethicon Llc | Surgical instrument with detection sensors |
US11607239B2 (en) | 2016-04-15 | 2023-03-21 | Cilag Gmbh International | Systems and methods for controlling a surgical stapling and cutting instrument |
US11317917B2 (en) | 2016-04-18 | 2022-05-03 | Cilag Gmbh International | Surgical stapling system comprising a lockable firing assembly |
US20170296173A1 (en) | 2016-04-18 | 2017-10-19 | Ethicon Endo-Surgery, Llc | Method for operating a surgical instrument |
US10426469B2 (en) | 2016-04-18 | 2019-10-01 | Ethicon Llc | Surgical instrument comprising a primary firing lockout and a secondary firing lockout |
CN105748069B (en) * | 2016-04-21 | 2018-10-23 | 罗远明 | A kind of centric sleep apnea carbon dioxide inhalation therapy device |
US11160948B2 (en) * | 2016-06-22 | 2021-11-02 | Imam Abdulrahman Bin Faisal University | Nebulizer tubing with a port to minimize medicament loss |
ES2894895T3 (en) | 2016-07-08 | 2022-02-16 | Trudell Medical Int | Intelligent oscillating positive expiratory pressure device |
US10080521B2 (en) | 2016-08-01 | 2018-09-25 | Timothy Joshua Parrish | Sleep apnea bi-level positive airway pressure machine with advanced diagnostics and self-cleaning capabilities |
CA3036631A1 (en) | 2016-12-09 | 2018-06-14 | Trudell Medical International | Smart nebulizer |
US10888322B2 (en) | 2016-12-21 | 2021-01-12 | Ethicon Llc | Surgical instrument comprising a cutting member |
US10568624B2 (en) | 2016-12-21 | 2020-02-25 | Ethicon Llc | Surgical instruments with jaws that are pivotable about a fixed axis and include separate and distinct closure and firing systems |
US11191540B2 (en) | 2016-12-21 | 2021-12-07 | Cilag Gmbh International | Protective cover arrangements for a joint interface between a movable jaw and actuator shaft of a surgical instrument |
US11134942B2 (en) | 2016-12-21 | 2021-10-05 | Cilag Gmbh International | Surgical stapling instruments and staple-forming anvils |
MX2019007311A (en) | 2016-12-21 | 2019-11-18 | Ethicon Llc | Surgical stapling systems. |
JP6983893B2 (en) | 2016-12-21 | 2021-12-17 | エシコン エルエルシーEthicon LLC | Lockout configuration for surgical end effectors and replaceable tool assemblies |
US11419606B2 (en) | 2016-12-21 | 2022-08-23 | Cilag Gmbh International | Shaft assembly comprising a clutch configured to adapt the output of a rotary firing member to two different systems |
US10856868B2 (en) | 2016-12-21 | 2020-12-08 | Ethicon Llc | Firing member pin configurations |
JP7010956B2 (en) | 2016-12-21 | 2022-01-26 | エシコン エルエルシー | How to staple tissue |
US10588630B2 (en) | 2016-12-21 | 2020-03-17 | Ethicon Llc | Surgical tool assemblies with closure stroke reduction features |
US10568625B2 (en) | 2016-12-21 | 2020-02-25 | Ethicon Llc | Staple cartridges and arrangements of staples and staple cavities therein |
US10426471B2 (en) | 2016-12-21 | 2019-10-01 | Ethicon Llc | Surgical instrument with multiple failure response modes |
US20180168598A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Staple forming pocket arrangements comprising zoned forming surface grooves |
US20180168625A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Surgical stapling instruments with smart staple cartridges |
US20180168615A1 (en) | 2016-12-21 | 2018-06-21 | Ethicon Endo-Surgery, Llc | Method of deforming staples from two different types of staple cartridges with the same surgical stapling instrument |
US11090048B2 (en) | 2016-12-21 | 2021-08-17 | Cilag Gmbh International | Method for resetting a fuse of a surgical instrument shaft |
US10675025B2 (en) | 2016-12-21 | 2020-06-09 | Ethicon Llc | Shaft assembly comprising separately actuatable and retractable systems |
US10610224B2 (en) | 2016-12-21 | 2020-04-07 | Ethicon Llc | Lockout arrangements for surgical end effectors and replaceable tool assemblies |
US10695055B2 (en) | 2016-12-21 | 2020-06-30 | Ethicon Llc | Firing assembly comprising a lockout |
US10532175B1 (en) * | 2019-05-23 | 2020-01-14 | Model Software Corporation | Methods for minimizing delayed effects of exposure to reduced oxygen partial pressure via administration of supplemental oxygen |
US11617847B2 (en) | 2017-01-11 | 2023-04-04 | Model Software Corporation | Methods for minimizing delayed effects of exposure to reduced oxygen partial pressure via administration of supplemental oxygen |
US11382638B2 (en) | 2017-06-20 | 2022-07-12 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured time over a specified displacement distance |
US10813639B2 (en) | 2017-06-20 | 2020-10-27 | Ethicon Llc | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on system conditions |
USD879809S1 (en) | 2017-06-20 | 2020-03-31 | Ethicon Llc | Display panel with changeable graphical user interface |
US10888321B2 (en) | 2017-06-20 | 2021-01-12 | Ethicon Llc | Systems and methods for controlling velocity of a displacement member of a surgical stapling and cutting instrument |
US10779820B2 (en) | 2017-06-20 | 2020-09-22 | Ethicon Llc | Systems and methods for controlling motor speed according to user input for a surgical instrument |
US10368864B2 (en) | 2017-06-20 | 2019-08-06 | Ethicon Llc | Systems and methods for controlling displaying motor velocity for a surgical instrument |
US10881399B2 (en) | 2017-06-20 | 2021-01-05 | Ethicon Llc | Techniques for adaptive control of motor velocity of a surgical stapling and cutting instrument |
US10327767B2 (en) | 2017-06-20 | 2019-06-25 | Ethicon Llc | Control of motor velocity of a surgical stapling and cutting instrument based on angle of articulation |
USD879808S1 (en) | 2017-06-20 | 2020-03-31 | Ethicon Llc | Display panel with graphical user interface |
US10307170B2 (en) | 2017-06-20 | 2019-06-04 | Ethicon Llc | Method for closed loop control of motor velocity of a surgical stapling and cutting instrument |
US11653914B2 (en) | 2017-06-20 | 2023-05-23 | Cilag Gmbh International | Systems and methods for controlling motor velocity of a surgical stapling and cutting instrument according to articulation angle of end effector |
US10980537B2 (en) | 2017-06-20 | 2021-04-20 | Ethicon Llc | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured time over a specified number of shaft rotations |
US11517325B2 (en) | 2017-06-20 | 2022-12-06 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on measured displacement distance traveled over a specified time interval |
USD890784S1 (en) | 2017-06-20 | 2020-07-21 | Ethicon Llc | Display panel with changeable graphical user interface |
US11071554B2 (en) | 2017-06-20 | 2021-07-27 | Cilag Gmbh International | Closed loop feedback control of motor velocity of a surgical stapling and cutting instrument based on magnitude of velocity error measurements |
US10624633B2 (en) | 2017-06-20 | 2020-04-21 | Ethicon Llc | Systems and methods for controlling motor velocity of a surgical stapling and cutting instrument |
US10881396B2 (en) | 2017-06-20 | 2021-01-05 | Ethicon Llc | Surgical instrument with variable duration trigger arrangement |
US11090046B2 (en) | 2017-06-20 | 2021-08-17 | Cilag Gmbh International | Systems and methods for controlling displacement member motion of a surgical stapling and cutting instrument |
US10390841B2 (en) | 2017-06-20 | 2019-08-27 | Ethicon Llc | Control of motor velocity of a surgical stapling and cutting instrument based on angle of articulation |
US10646220B2 (en) | 2017-06-20 | 2020-05-12 | Ethicon Llc | Systems and methods for controlling displacement member velocity for a surgical instrument |
US10993716B2 (en) | 2017-06-27 | 2021-05-04 | Ethicon Llc | Surgical anvil arrangements |
US10856869B2 (en) | 2017-06-27 | 2020-12-08 | Ethicon Llc | Surgical anvil arrangements |
US11266405B2 (en) | 2017-06-27 | 2022-03-08 | Cilag Gmbh International | Surgical anvil manufacturing methods |
US10631859B2 (en) | 2017-06-27 | 2020-04-28 | Ethicon Llc | Articulation systems for surgical instruments |
US10772629B2 (en) | 2017-06-27 | 2020-09-15 | Ethicon Llc | Surgical anvil arrangements |
US11324503B2 (en) | 2017-06-27 | 2022-05-10 | Cilag Gmbh International | Surgical firing member arrangements |
USD851762S1 (en) | 2017-06-28 | 2019-06-18 | Ethicon Llc | Anvil |
USD854151S1 (en) | 2017-06-28 | 2019-07-16 | Ethicon Llc | Surgical instrument shaft |
US10765427B2 (en) | 2017-06-28 | 2020-09-08 | Ethicon Llc | Method for articulating a surgical instrument |
US10211586B2 (en) | 2017-06-28 | 2019-02-19 | Ethicon Llc | Surgical shaft assemblies with watertight housings |
USD869655S1 (en) | 2017-06-28 | 2019-12-10 | Ethicon Llc | Surgical fastener cartridge |
US11259805B2 (en) | 2017-06-28 | 2022-03-01 | Cilag Gmbh International | Surgical instrument comprising firing member supports |
US20190000461A1 (en) | 2017-06-28 | 2019-01-03 | Ethicon Llc | Surgical cutting and fastening devices with pivotable anvil with a tissue locating arrangement in close proximity to an anvil pivot axis |
EP4070740A1 (en) | 2017-06-28 | 2022-10-12 | Cilag GmbH International | Surgical instrument comprising selectively actuatable rotatable couplers |
US11564686B2 (en) | 2017-06-28 | 2023-01-31 | Cilag Gmbh International | Surgical shaft assemblies with flexible interfaces |
USD906355S1 (en) | 2017-06-28 | 2020-12-29 | Ethicon Llc | Display screen or portion thereof with a graphical user interface for a surgical instrument |
US10716614B2 (en) | 2017-06-28 | 2020-07-21 | Ethicon Llc | Surgical shaft assemblies with slip ring assemblies with increased contact pressure |
US10903685B2 (en) | 2017-06-28 | 2021-01-26 | Ethicon Llc | Surgical shaft assemblies with slip ring assemblies forming capacitive channels |
US11678880B2 (en) | 2017-06-28 | 2023-06-20 | Cilag Gmbh International | Surgical instrument comprising a shaft including a housing arrangement |
US11246592B2 (en) | 2017-06-28 | 2022-02-15 | Cilag Gmbh International | Surgical instrument comprising an articulation system lockable to a frame |
US10932772B2 (en) | 2017-06-29 | 2021-03-02 | Ethicon Llc | Methods for closed loop velocity control for robotic surgical instrument |
US11007022B2 (en) | 2017-06-29 | 2021-05-18 | Ethicon Llc | Closed loop velocity control techniques based on sensed tissue parameters for robotic surgical instrument |
US10398434B2 (en) | 2017-06-29 | 2019-09-03 | Ethicon Llc | Closed loop velocity control of closure member for robotic surgical instrument |
US10258418B2 (en) | 2017-06-29 | 2019-04-16 | Ethicon Llc | System for controlling articulation forces |
US10898183B2 (en) | 2017-06-29 | 2021-01-26 | Ethicon Llc | Robotic surgical instrument with closed loop feedback techniques for advancement of closure member during firing |
US11944300B2 (en) | 2017-08-03 | 2024-04-02 | Cilag Gmbh International | Method for operating a surgical system bailout |
US11304695B2 (en) | 2017-08-03 | 2022-04-19 | Cilag Gmbh International | Surgical system shaft interconnection |
US11471155B2 (en) | 2017-08-03 | 2022-10-18 | Cilag Gmbh International | Surgical system bailout |
US10765429B2 (en) | 2017-09-29 | 2020-09-08 | Ethicon Llc | Systems and methods for providing alerts according to the operational state of a surgical instrument |
USD907648S1 (en) | 2017-09-29 | 2021-01-12 | Ethicon Llc | Display screen or portion thereof with animated graphical user interface |
USD917500S1 (en) | 2017-09-29 | 2021-04-27 | Ethicon Llc | Display screen or portion thereof with graphical user interface |
US11399829B2 (en) | 2017-09-29 | 2022-08-02 | Cilag Gmbh International | Systems and methods of initiating a power shutdown mode for a surgical instrument |
US10796471B2 (en) | 2017-09-29 | 2020-10-06 | Ethicon Llc | Systems and methods of displaying a knife position for a surgical instrument |
US10743872B2 (en) | 2017-09-29 | 2020-08-18 | Ethicon Llc | System and methods for controlling a display of a surgical instrument |
US10729501B2 (en) | 2017-09-29 | 2020-08-04 | Ethicon Llc | Systems and methods for language selection of a surgical instrument |
USD907647S1 (en) | 2017-09-29 | 2021-01-12 | Ethicon Llc | Display screen or portion thereof with animated graphical user interface |
US10792449B2 (en) | 2017-10-03 | 2020-10-06 | Breathe Technologies, Inc. | Patient interface with integrated jet pump |
US11090075B2 (en) | 2017-10-30 | 2021-08-17 | Cilag Gmbh International | Articulation features for surgical end effector |
US11134944B2 (en) | 2017-10-30 | 2021-10-05 | Cilag Gmbh International | Surgical stapler knife motion controls |
US10842490B2 (en) | 2017-10-31 | 2020-11-24 | Ethicon Llc | Cartridge body design with force reduction based on firing completion |
US10779903B2 (en) | 2017-10-31 | 2020-09-22 | Ethicon Llc | Positive shaft rotation lock activated by jaw closure |
US10779826B2 (en) | 2017-12-15 | 2020-09-22 | Ethicon Llc | Methods of operating surgical end effectors |
US11197670B2 (en) | 2017-12-15 | 2021-12-14 | Cilag Gmbh International | Surgical end effectors with pivotal jaws configured to touch at their respective distal ends when fully closed |
US10828033B2 (en) | 2017-12-15 | 2020-11-10 | Ethicon Llc | Handheld electromechanical surgical instruments with improved motor control arrangements for positioning components of an adapter coupled thereto |
US10743875B2 (en) | 2017-12-15 | 2020-08-18 | Ethicon Llc | Surgical end effectors with jaw stiffener arrangements configured to permit monitoring of firing member |
US10779825B2 (en) | 2017-12-15 | 2020-09-22 | Ethicon Llc | Adapters with end effector position sensing and control arrangements for use in connection with electromechanical surgical instruments |
US10687813B2 (en) | 2017-12-15 | 2020-06-23 | Ethicon Llc | Adapters with firing stroke sensing arrangements for use in connection with electromechanical surgical instruments |
US11033267B2 (en) | 2017-12-15 | 2021-06-15 | Ethicon Llc | Systems and methods of controlling a clamping member firing rate of a surgical instrument |
US11071543B2 (en) | 2017-12-15 | 2021-07-27 | Cilag Gmbh International | Surgical end effectors with clamping assemblies configured to increase jaw aperture ranges |
US10966718B2 (en) | 2017-12-15 | 2021-04-06 | Ethicon Llc | Dynamic clamping assemblies with improved wear characteristics for use in connection with electromechanical surgical instruments |
US10869666B2 (en) | 2017-12-15 | 2020-12-22 | Ethicon Llc | Adapters with control systems for controlling multiple motors of an electromechanical surgical instrument |
US10743874B2 (en) | 2017-12-15 | 2020-08-18 | Ethicon Llc | Sealed adapters for use with electromechanical surgical instruments |
US11006955B2 (en) | 2017-12-15 | 2021-05-18 | Ethicon Llc | End effectors with positive jaw opening features for use with adapters for electromechanical surgical instruments |
US11020112B2 (en) | 2017-12-19 | 2021-06-01 | Ethicon Llc | Surgical tools configured for interchangeable use with different controller interfaces |
US10835330B2 (en) | 2017-12-19 | 2020-11-17 | Ethicon Llc | Method for determining the position of a rotatable jaw of a surgical instrument attachment assembly |
US11045270B2 (en) | 2017-12-19 | 2021-06-29 | Cilag Gmbh International | Robotic attachment comprising exterior drive actuator |
USD910847S1 (en) | 2017-12-19 | 2021-02-16 | Ethicon Llc | Surgical instrument assembly |
US10729509B2 (en) | 2017-12-19 | 2020-08-04 | Ethicon Llc | Surgical instrument comprising closure and firing locking mechanism |
US10716565B2 (en) | 2017-12-19 | 2020-07-21 | Ethicon Llc | Surgical instruments with dual articulation drivers |
US11129680B2 (en) | 2017-12-21 | 2021-09-28 | Cilag Gmbh International | Surgical instrument comprising a projector |
US11076853B2 (en) | 2017-12-21 | 2021-08-03 | Cilag Gmbh International | Systems and methods of displaying a knife position during transection for a surgical instrument |
US11311290B2 (en) | 2017-12-21 | 2022-04-26 | Cilag Gmbh International | Surgical instrument comprising an end effector dampener |
US11337691B2 (en) | 2017-12-21 | 2022-05-24 | Cilag Gmbh International | Surgical instrument configured to determine firing path |
AU2019205865A1 (en) | 2018-01-04 | 2020-07-16 | Trudell Medical International Inc. | Smart oscillating positive expiratory pressure device |
EP3793656A1 (en) | 2018-05-14 | 2021-03-24 | Covidien LP | Systems and methods for respiratory effort detection utilizing signal distortion |
US11141553B2 (en) * | 2018-07-11 | 2021-10-12 | General Electric Company | Ventilation control system and method utilizing patient oxygen saturation |
US11253256B2 (en) | 2018-08-20 | 2022-02-22 | Cilag Gmbh International | Articulatable motor powered surgical instruments with dedicated articulation motor arrangements |
US10842492B2 (en) | 2018-08-20 | 2020-11-24 | Ethicon Llc | Powered articulatable surgical instruments with clutching and locking arrangements for linking an articulation drive system to a firing drive system |
USD914878S1 (en) | 2018-08-20 | 2021-03-30 | Ethicon Llc | Surgical instrument anvil |
US11083458B2 (en) | 2018-08-20 | 2021-08-10 | Cilag Gmbh International | Powered surgical instruments with clutching arrangements to convert linear drive motions to rotary drive motions |
US10912559B2 (en) | 2018-08-20 | 2021-02-09 | Ethicon Llc | Reinforced deformable anvil tip for surgical stapler anvil |
US11291440B2 (en) | 2018-08-20 | 2022-04-05 | Cilag Gmbh International | Method for operating a powered articulatable surgical instrument |
US11045192B2 (en) | 2018-08-20 | 2021-06-29 | Cilag Gmbh International | Fabricating techniques for surgical stapler anvils |
US10856870B2 (en) | 2018-08-20 | 2020-12-08 | Ethicon Llc | Switching arrangements for motor powered articulatable surgical instruments |
US10779821B2 (en) | 2018-08-20 | 2020-09-22 | Ethicon Llc | Surgical stapler anvils with tissue stop features configured to avoid tissue pinch |
US11324501B2 (en) | 2018-08-20 | 2022-05-10 | Cilag Gmbh International | Surgical stapling devices with improved closure members |
US11207065B2 (en) | 2018-08-20 | 2021-12-28 | Cilag Gmbh International | Method for fabricating surgical stapler anvils |
US11039834B2 (en) | 2018-08-20 | 2021-06-22 | Cilag Gmbh International | Surgical stapler anvils with staple directing protrusions and tissue stability features |
US11752287B2 (en) | 2018-10-03 | 2023-09-12 | Covidien Lp | Systems and methods for automatic cycling or cycling detection |
WO2020186085A1 (en) * | 2019-03-12 | 2020-09-17 | Live Fully, Inc. | Oxygen monitoring and control system |
US11147551B2 (en) | 2019-03-25 | 2021-10-19 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11172929B2 (en) | 2019-03-25 | 2021-11-16 | Cilag Gmbh International | Articulation drive arrangements for surgical systems |
US11696761B2 (en) | 2019-03-25 | 2023-07-11 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11147553B2 (en) | 2019-03-25 | 2021-10-19 | Cilag Gmbh International | Firing drive arrangements for surgical systems |
US11903581B2 (en) | 2019-04-30 | 2024-02-20 | Cilag Gmbh International | Methods for stapling tissue using a surgical instrument |
US11648009B2 (en) | 2019-04-30 | 2023-05-16 | Cilag Gmbh International | Rotatable jaw tip for a surgical instrument |
US11432816B2 (en) | 2019-04-30 | 2022-09-06 | Cilag Gmbh International | Articulation pin for a surgical instrument |
US11452528B2 (en) | 2019-04-30 | 2022-09-27 | Cilag Gmbh International | Articulation actuators for a surgical instrument |
US11253254B2 (en) | 2019-04-30 | 2022-02-22 | Cilag Gmbh International | Shaft rotation actuator on a surgical instrument |
US11426251B2 (en) | 2019-04-30 | 2022-08-30 | Cilag Gmbh International | Articulation directional lights on a surgical instrument |
US11471157B2 (en) | 2019-04-30 | 2022-10-18 | Cilag Gmbh International | Articulation control mapping for a surgical instrument |
US11627959B2 (en) | 2019-06-28 | 2023-04-18 | Cilag Gmbh International | Surgical instruments including manual and powered system lockouts |
US11771419B2 (en) | 2019-06-28 | 2023-10-03 | Cilag Gmbh International | Packaging for a replaceable component of a surgical stapling system |
US11291451B2 (en) | 2019-06-28 | 2022-04-05 | Cilag Gmbh International | Surgical instrument with battery compatibility verification functionality |
US11660163B2 (en) | 2019-06-28 | 2023-05-30 | Cilag Gmbh International | Surgical system with RFID tags for updating motor assembly parameters |
US11426167B2 (en) | 2019-06-28 | 2022-08-30 | Cilag Gmbh International | Mechanisms for proper anvil attachment surgical stapling head assembly |
US11497492B2 (en) | 2019-06-28 | 2022-11-15 | Cilag Gmbh International | Surgical instrument including an articulation lock |
US11684434B2 (en) | 2019-06-28 | 2023-06-27 | Cilag Gmbh International | Surgical RFID assemblies for instrument operational setting control |
US11224497B2 (en) | 2019-06-28 | 2022-01-18 | Cilag Gmbh International | Surgical systems with multiple RFID tags |
US11399837B2 (en) | 2019-06-28 | 2022-08-02 | Cilag Gmbh International | Mechanisms for motor control adjustments of a motorized surgical instrument |
US11298127B2 (en) | 2019-06-28 | 2022-04-12 | Cilag GmbH Interational | Surgical stapling system having a lockout mechanism for an incompatible cartridge |
US11464601B2 (en) | 2019-06-28 | 2022-10-11 | Cilag Gmbh International | Surgical instrument comprising an RFID system for tracking a movable component |
US11219455B2 (en) | 2019-06-28 | 2022-01-11 | Cilag Gmbh International | Surgical instrument including a lockout key |
US11298132B2 (en) | 2019-06-28 | 2022-04-12 | Cilag GmbH Inlernational | Staple cartridge including a honeycomb extension |
US11241235B2 (en) | 2019-06-28 | 2022-02-08 | Cilag Gmbh International | Method of using multiple RFID chips with a surgical assembly |
US11523822B2 (en) | 2019-06-28 | 2022-12-13 | Cilag Gmbh International | Battery pack including a circuit interrupter |
US11376098B2 (en) | 2019-06-28 | 2022-07-05 | Cilag Gmbh International | Surgical instrument system comprising an RFID system |
US11478241B2 (en) | 2019-06-28 | 2022-10-25 | Cilag Gmbh International | Staple cartridge including projections |
US11553971B2 (en) | 2019-06-28 | 2023-01-17 | Cilag Gmbh International | Surgical RFID assemblies for display and communication |
US11638587B2 (en) | 2019-06-28 | 2023-05-02 | Cilag Gmbh International | RFID identification systems for surgical instruments |
US11259803B2 (en) | 2019-06-28 | 2022-03-01 | Cilag Gmbh International | Surgical stapling system having an information encryption protocol |
US11246678B2 (en) | 2019-06-28 | 2022-02-15 | Cilag Gmbh International | Surgical stapling system having a frangible RFID tag |
US11051807B2 (en) | 2019-06-28 | 2021-07-06 | Cilag Gmbh International | Packaging assembly including a particulate trap |
CA3152072A1 (en) | 2019-08-27 | 2021-03-04 | Trudell Medical International | Smart oscillating positive expiratory pressure device |
US11779720B2 (en) | 2019-11-04 | 2023-10-10 | Vapotherm, Inc. | Methods, devices, and systems for improved oxygenation patient monitoring, mixing, and delivery |
US11612706B2 (en) | 2019-11-25 | 2023-03-28 | John C. Taube | Methods, systems, and devices for controlling mechanical ventilation |
US11559304B2 (en) | 2019-12-19 | 2023-01-24 | Cilag Gmbh International | Surgical instrument comprising a rapid closure mechanism |
US11234698B2 (en) | 2019-12-19 | 2022-02-01 | Cilag Gmbh International | Stapling system comprising a clamp lockout and a firing lockout |
US11446029B2 (en) | 2019-12-19 | 2022-09-20 | Cilag Gmbh International | Staple cartridge comprising projections extending from a curved deck surface |
US11701111B2 (en) | 2019-12-19 | 2023-07-18 | Cilag Gmbh International | Method for operating a surgical stapling instrument |
US11844520B2 (en) | 2019-12-19 | 2023-12-19 | Cilag Gmbh International | Staple cartridge comprising driver retention members |
US11304696B2 (en) | 2019-12-19 | 2022-04-19 | Cilag Gmbh International | Surgical instrument comprising a powered articulation system |
US11464512B2 (en) | 2019-12-19 | 2022-10-11 | Cilag Gmbh International | Staple cartridge comprising a curved deck surface |
US11504122B2 (en) | 2019-12-19 | 2022-11-22 | Cilag Gmbh International | Surgical instrument comprising a nested firing member |
US11607219B2 (en) | 2019-12-19 | 2023-03-21 | Cilag Gmbh International | Staple cartridge comprising a detachable tissue cutting knife |
US11529137B2 (en) | 2019-12-19 | 2022-12-20 | Cilag Gmbh International | Staple cartridge comprising driver retention members |
US11931033B2 (en) | 2019-12-19 | 2024-03-19 | Cilag Gmbh International | Staple cartridge comprising a latch lockout |
US11911032B2 (en) | 2019-12-19 | 2024-02-27 | Cilag Gmbh International | Staple cartridge comprising a seating cam |
US11529139B2 (en) | 2019-12-19 | 2022-12-20 | Cilag Gmbh International | Motor driven surgical instrument |
US11291447B2 (en) | 2019-12-19 | 2022-04-05 | Cilag Gmbh International | Stapling instrument comprising independent jaw closing and staple firing systems |
US11576672B2 (en) | 2019-12-19 | 2023-02-14 | Cilag Gmbh International | Surgical instrument comprising a closure system including a closure member and an opening member driven by a drive screw |
USD967421S1 (en) | 2020-06-02 | 2022-10-18 | Cilag Gmbh International | Staple cartridge |
USD975278S1 (en) | 2020-06-02 | 2023-01-10 | Cilag Gmbh International | Staple cartridge |
USD974560S1 (en) | 2020-06-02 | 2023-01-03 | Cilag Gmbh International | Staple cartridge |
USD976401S1 (en) | 2020-06-02 | 2023-01-24 | Cilag Gmbh International | Staple cartridge |
USD975851S1 (en) | 2020-06-02 | 2023-01-17 | Cilag Gmbh International | Staple cartridge |
USD966512S1 (en) | 2020-06-02 | 2022-10-11 | Cilag Gmbh International | Staple cartridge |
USD975850S1 (en) | 2020-06-02 | 2023-01-17 | Cilag Gmbh International | Staple cartridge |
CA3189534A1 (en) | 2020-07-16 | 2022-01-20 | Invacare Corporation | System and method for concentrating gas |
CA3189540A1 (en) | 2020-07-16 | 2022-01-20 | Invacare Corporation | System and method for concentrating gas |
US11883024B2 (en) | 2020-07-28 | 2024-01-30 | Cilag Gmbh International | Method of operating a surgical instrument |
US11247008B1 (en) | 2020-08-05 | 2022-02-15 | Effortless Oxygen, Llc | Flow triggered gas delivery |
US11318276B2 (en) | 2020-08-05 | 2022-05-03 | Effortless Oxygen, Llc | Flow triggered gas delivery |
US11420007B2 (en) | 2020-08-05 | 2022-08-23 | Effortless Oxygen, Llc | Flow triggered gas delivery |
CN112245731B (en) * | 2020-10-19 | 2022-10-11 | 湖南万脉医疗科技有限公司 | Aerator for breathing machine and application thereof |
US11896217B2 (en) | 2020-10-29 | 2024-02-13 | Cilag Gmbh International | Surgical instrument comprising an articulation lock |
US11717289B2 (en) | 2020-10-29 | 2023-08-08 | Cilag Gmbh International | Surgical instrument comprising an indicator which indicates that an articulation drive is actuatable |
USD1013170S1 (en) | 2020-10-29 | 2024-01-30 | Cilag Gmbh International | Surgical instrument assembly |
US11617577B2 (en) | 2020-10-29 | 2023-04-04 | Cilag Gmbh International | Surgical instrument comprising a sensor configured to sense whether an articulation drive of the surgical instrument is actuatable |
US11844518B2 (en) | 2020-10-29 | 2023-12-19 | Cilag Gmbh International | Method for operating a surgical instrument |
US11779330B2 (en) | 2020-10-29 | 2023-10-10 | Cilag Gmbh International | Surgical instrument comprising a jaw alignment system |
US11452526B2 (en) | 2020-10-29 | 2022-09-27 | Cilag Gmbh International | Surgical instrument comprising a staged voltage regulation start-up system |
USD980425S1 (en) | 2020-10-29 | 2023-03-07 | Cilag Gmbh International | Surgical instrument assembly |
US11517390B2 (en) | 2020-10-29 | 2022-12-06 | Cilag Gmbh International | Surgical instrument comprising a limited travel switch |
US11534259B2 (en) | 2020-10-29 | 2022-12-27 | Cilag Gmbh International | Surgical instrument comprising an articulation indicator |
US11931025B2 (en) | 2020-10-29 | 2024-03-19 | Cilag Gmbh International | Surgical instrument comprising a releasable closure drive lock |
US11944296B2 (en) | 2020-12-02 | 2024-04-02 | Cilag Gmbh International | Powered surgical instruments with external connectors |
US11890010B2 (en) | 2020-12-02 | 2024-02-06 | Cllag GmbH International | Dual-sided reinforced reload for surgical instruments |
US11744581B2 (en) | 2020-12-02 | 2023-09-05 | Cilag Gmbh International | Powered surgical instruments with multi-phase tissue treatment |
US11737751B2 (en) | 2020-12-02 | 2023-08-29 | Cilag Gmbh International | Devices and methods of managing energy dissipated within sterile barriers of surgical instrument housings |
US11627960B2 (en) | 2020-12-02 | 2023-04-18 | Cilag Gmbh International | Powered surgical instruments with smart reload with separately attachable exteriorly mounted wiring connections |
US11678882B2 (en) | 2020-12-02 | 2023-06-20 | Cilag Gmbh International | Surgical instruments with interactive features to remedy incidental sled movements |
US11849943B2 (en) | 2020-12-02 | 2023-12-26 | Cilag Gmbh International | Surgical instrument with cartridge release mechanisms |
US11653915B2 (en) | 2020-12-02 | 2023-05-23 | Cilag Gmbh International | Surgical instruments with sled location detection and adjustment features |
US11653920B2 (en) | 2020-12-02 | 2023-05-23 | Cilag Gmbh International | Powered surgical instruments with communication interfaces through sterile barrier |
US11749877B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Stapling instrument comprising a signal antenna |
US11925349B2 (en) | 2021-02-26 | 2024-03-12 | Cilag Gmbh International | Adjustment to transfer parameters to improve available power |
US11730473B2 (en) | 2021-02-26 | 2023-08-22 | Cilag Gmbh International | Monitoring of manufacturing life-cycle |
US11744583B2 (en) | 2021-02-26 | 2023-09-05 | Cilag Gmbh International | Distal communication array to tune frequency of RF systems |
US11751869B2 (en) | 2021-02-26 | 2023-09-12 | Cilag Gmbh International | Monitoring of multiple sensors over time to detect moving characteristics of tissue |
US11793514B2 (en) | 2021-02-26 | 2023-10-24 | Cilag Gmbh International | Staple cartridge comprising sensor array which may be embedded in cartridge body |
US11950777B2 (en) | 2021-02-26 | 2024-04-09 | Cilag Gmbh International | Staple cartridge comprising an information access control system |
US11696757B2 (en) | 2021-02-26 | 2023-07-11 | Cilag Gmbh International | Monitoring of internal systems to detect and track cartridge motion status |
US11701113B2 (en) | 2021-02-26 | 2023-07-18 | Cilag Gmbh International | Stapling instrument comprising a separate power antenna and a data transfer antenna |
US11723657B2 (en) | 2021-02-26 | 2023-08-15 | Cilag Gmbh International | Adjustable communication based on available bandwidth and power capacity |
US11812964B2 (en) | 2021-02-26 | 2023-11-14 | Cilag Gmbh International | Staple cartridge comprising a power management circuit |
US11950779B2 (en) | 2021-02-26 | 2024-04-09 | Cilag Gmbh International | Method of powering and communicating with a staple cartridge |
US11826042B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Surgical instrument comprising a firing drive including a selectable leverage mechanism |
US11826012B2 (en) | 2021-03-22 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising a pulsed motor-driven firing rack |
US11723658B2 (en) | 2021-03-22 | 2023-08-15 | Cilag Gmbh International | Staple cartridge comprising a firing lockout |
US11806011B2 (en) | 2021-03-22 | 2023-11-07 | Cilag Gmbh International | Stapling instrument comprising tissue compression systems |
US11737749B2 (en) | 2021-03-22 | 2023-08-29 | Cilag Gmbh International | Surgical stapling instrument comprising a retraction system |
US11759202B2 (en) | 2021-03-22 | 2023-09-19 | Cilag Gmbh International | Staple cartridge comprising an implantable layer |
US11717291B2 (en) | 2021-03-22 | 2023-08-08 | Cilag Gmbh International | Staple cartridge comprising staples configured to apply different tissue compression |
US11944336B2 (en) | 2021-03-24 | 2024-04-02 | Cilag Gmbh International | Joint arrangements for multi-planar alignment and support of operational drive shafts in articulatable surgical instruments |
US11849945B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Rotary-driven surgical stapling assembly comprising eccentrically driven firing member |
US11832816B2 (en) | 2021-03-24 | 2023-12-05 | Cilag Gmbh International | Surgical stapling assembly comprising nonplanar staples and planar staples |
US11903582B2 (en) | 2021-03-24 | 2024-02-20 | Cilag Gmbh International | Leveraging surfaces for cartridge installation |
US11793516B2 (en) | 2021-03-24 | 2023-10-24 | Cilag Gmbh International | Surgical staple cartridge comprising longitudinal support beam |
US11786243B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Firing members having flexible portions for adapting to a load during a surgical firing stroke |
US11744603B2 (en) | 2021-03-24 | 2023-09-05 | Cilag Gmbh International | Multi-axis pivot joints for surgical instruments and methods for manufacturing same |
US11786239B2 (en) | 2021-03-24 | 2023-10-17 | Cilag Gmbh International | Surgical instrument articulation joint arrangements comprising multiple moving linkage features |
US11849944B2 (en) | 2021-03-24 | 2023-12-26 | Cilag Gmbh International | Drivers for fastener cartridge assemblies having rotary drive screws |
US11896219B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Mating features between drivers and underside of a cartridge deck |
US11896218B2 (en) | 2021-03-24 | 2024-02-13 | Cilag Gmbh International | Method of using a powered stapling device |
US11857183B2 (en) | 2021-03-24 | 2024-01-02 | Cilag Gmbh International | Stapling assembly components having metal substrates and plastic bodies |
WO2022244004A1 (en) * | 2021-05-20 | 2022-11-24 | Ravit Barkama | Systems and methods for supplemental oxygen delivery |
US11826047B2 (en) | 2021-05-28 | 2023-11-28 | Cilag Gmbh International | Stapling instrument comprising jaw mounts |
US11877745B2 (en) | 2021-10-18 | 2024-01-23 | Cilag Gmbh International | Surgical stapling assembly having longitudinally-repeating staple leg clusters |
US11957337B2 (en) | 2021-10-18 | 2024-04-16 | Cilag Gmbh International | Surgical stapling assembly with offset ramped drive surfaces |
US11937816B2 (en) | 2021-10-28 | 2024-03-26 | Cilag Gmbh International | Electrical lead arrangements for surgical instruments |
Citations (91)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2414747A (en) * | 1942-07-02 | 1947-01-21 | Harry M Kirschbaum | Method and apparatus for controlling the oxygen content of the blood of living animals |
US2912979A (en) * | 1956-02-17 | 1959-11-17 | Lieber Samuel Loewenstein | Apparatus for administering and conserving gas |
US3400713A (en) * | 1966-10-12 | 1968-09-10 | James E. Finan | Apparatus for intermittently dispensing oxygen or other gas suitable for breathing |
US3400712A (en) * | 1965-08-12 | 1968-09-10 | James E. Finan | System for intermittently dispensing oxygen or other gas suitable for breathing |
US3493703A (en) * | 1968-08-02 | 1970-02-03 | James E Finan | Body motion sensitive electrical switch with lost motion means |
US3734091A (en) * | 1971-06-22 | 1973-05-22 | Airco Inc | Oxygen control system with blood oxygen saturation sensing means and method for closed system breathing |
US3834383A (en) * | 1972-12-11 | 1974-09-10 | Puritan Bennett Corp | Respiration apparatus with flow responsive control valve |
US4054133A (en) * | 1976-03-29 | 1977-10-18 | The Bendix Corporation | Control for a demand cannula |
US4278110A (en) * | 1979-11-13 | 1981-07-14 | Price Ernest H | Demand responsive flow controller |
US4326513A (en) * | 1979-07-02 | 1982-04-27 | Dragerwerk Ag | Patient data controlled respiration system |
US4336590A (en) * | 1979-05-02 | 1982-06-22 | Intertechnique | Devices for controlling gas flows |
US4381002A (en) * | 1980-12-18 | 1983-04-26 | The United States Of America As Represented By The Secretary Of The Army | Fluidic-controlled oxygen intermittent demand flow device |
US4457303A (en) * | 1980-11-26 | 1984-07-03 | Tritec Industries, Inc. | Respirating gas supply control method and apparatus therefor |
US4461293A (en) * | 1982-12-03 | 1984-07-24 | Kircaldie, Randall, And Mcnab | Respirating gas supply method and apparatus therefor |
US4484578A (en) * | 1980-11-26 | 1984-11-27 | Kircaldie, Randall And Mcnab | Respirator apparatus and method |
US4567888A (en) * | 1982-07-13 | 1986-02-04 | Compagnie Francaise De Produits Oxygenes | Device for treating respiratory deficiency of a patient |
US4575042A (en) * | 1984-08-17 | 1986-03-11 | Associates Of Dallas | Pneumatically amplified conservation valve |
US4584996A (en) * | 1984-03-12 | 1986-04-29 | Blum Alvin S | Apparatus for conservative supplemental oxygen therapy |
US4612928A (en) * | 1984-08-28 | 1986-09-23 | Tiep Brian L | Method and apparatus for supplying a gas to a body |
US4648395A (en) * | 1982-07-07 | 1987-03-10 | Sanyo Densihkogyo Co. Ltd. | Synchronized feed type oxygen concentrator for use in an open breathing system |
US4665911A (en) * | 1983-11-25 | 1987-05-19 | Electro-Fluidics | Intermittent supplemental oxygen apparatus and method |
US4681099A (en) * | 1984-11-30 | 1987-07-21 | Tottori University | Breath-synchronized concentrated-oxygen supplier |
US4686975A (en) * | 1985-05-03 | 1987-08-18 | Applied Membrane Technology, Inc. | Electronic respirable gas delivery device |
US4686974A (en) * | 1985-10-18 | 1987-08-18 | Tottori University | Breath synchronized gas-insufflation device and method therefor |
US4705034A (en) * | 1985-10-02 | 1987-11-10 | Perkins Warren E | Method and means for dispensing respirating gases by effecting a known displacement |
US4706664A (en) * | 1986-04-11 | 1987-11-17 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US4744356A (en) * | 1986-03-03 | 1988-05-17 | Greenwood Eugene C | Demand oxygen supply device |
US4745925A (en) * | 1986-10-06 | 1988-05-24 | Dietz Henry G | Optoelectronic inhalation sensor for monitoring inhalation and for inhalation therapy |
US4784130A (en) * | 1986-12-04 | 1988-11-15 | The John Bunn Company | Flow controller |
US4823788A (en) * | 1988-04-18 | 1989-04-25 | Smith Richard F M | Demand oxygen controller and respiratory monitor |
US4827922A (en) * | 1987-03-05 | 1989-05-09 | L'air Liquide | Process and device for supplying respiratory oxygen |
US4873971A (en) * | 1985-10-02 | 1989-10-17 | Perkins Warren E | Method and means for dispensing respirating gases by effecting a known displacement |
US4883353A (en) * | 1988-02-11 | 1989-11-28 | Puritan-Bennett Corporation | Pulse oximeter |
US4889116A (en) * | 1987-11-17 | 1989-12-26 | Phospho Energetics, Inc. | Adaptive control of neonatal fractional inspired oxygen |
US4932402A (en) * | 1986-04-11 | 1990-06-12 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US4971049A (en) * | 1989-11-06 | 1990-11-20 | Pulsair, Inc. | Pressure sensor control device for supplying oxygen |
US4972842A (en) * | 1988-06-09 | 1990-11-27 | Vital Signals, Inc. | Method and apparatus for precision monitoring of infants on assisted ventilation |
US5024219A (en) * | 1987-01-12 | 1991-06-18 | Dietz Henry G | Apparatus for inhalation therapy using triggered dose oxygenator employing an optoelectronic inhalation sensor |
US5038771A (en) * | 1990-01-25 | 1991-08-13 | Dietz Henry G | Method and apparatus for respiratory therapy using intermittent flow having automatic adjustment of a dose of therapeutic gas to the rate of breathing |
US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
US5052400A (en) * | 1986-02-20 | 1991-10-01 | Dietz Henry G | Method and apparatus for using an inhalation sensor for monitoring and for inhalation therapy |
US5074299A (en) * | 1988-05-02 | 1991-12-24 | Dietz Henry G | Monitor for controlling the flow of gases for breathing during inhalation |
US5099837A (en) * | 1990-09-28 | 1992-03-31 | Russel Sr Larry L | Inhalation-based control of medical gas |
US5103814A (en) * | 1988-04-28 | 1992-04-14 | Timothy Maher | Self-compensating patient respirator |
US5137017A (en) * | 1989-04-13 | 1992-08-11 | Salter Labs | Demand oxygen system |
US5165397A (en) * | 1988-12-15 | 1992-11-24 | Arp Leon J | Method and apparatus for demand oxygen system monitoring and control |
US5251632A (en) * | 1991-03-07 | 1993-10-12 | Hamamatsu Photonics K.K. | Tissue oxygen measuring system |
US5280780A (en) * | 1992-11-09 | 1994-01-25 | Abel Elaine R | Oxygen delivery and conserving device |
US5282464A (en) * | 1992-07-21 | 1994-02-01 | Brain Archibald Ian Jeremy | Combined laryngeal mask and reflectance oximeter |
US5315990A (en) * | 1991-12-30 | 1994-05-31 | Mondry Adolph J | Method for delivering incremental doses of oxygen for maximizing blood oxygen saturation levels |
US5323776A (en) * | 1992-10-15 | 1994-06-28 | Picker International, Inc. | MRI compatible pulse oximetry system |
US5360000A (en) * | 1987-03-19 | 1994-11-01 | Puritan-Bennett Corporation | Pneumatic demand oxygen valve |
US5365922A (en) * | 1991-03-19 | 1994-11-22 | Brigham And Women's Hospital, Inc. | Closed-loop non-invasive oxygen saturation control system |
US5388575A (en) * | 1992-09-25 | 1995-02-14 | Taube; John C. | Adaptive controller for automatic ventilators |
US5398676A (en) * | 1993-09-30 | 1995-03-21 | Press; Roman J. | Portable emergency respirator |
US5398682A (en) * | 1992-08-19 | 1995-03-21 | Lynn; Lawrence A. | Method and apparatus for the diagnosis of sleep apnea utilizing a single interface with a human body part |
US5429123A (en) * | 1993-12-15 | 1995-07-04 | Temple University - Of The Commonwealth System Of Higher Education | Process control and apparatus for ventilation procedures with helium and oxygen mixtures |
US5438980A (en) * | 1993-01-12 | 1995-08-08 | Puritan-Bennett Corporation | Inhalation/exhalation respiratory phase detection circuit |
US5443062A (en) * | 1993-11-23 | 1995-08-22 | Hayes; Jeffrey P. | Load activated oxygen delivery system |
US5490502A (en) * | 1992-05-07 | 1996-02-13 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5495848A (en) * | 1994-11-25 | 1996-03-05 | Nellcar Puritan Bennett | Monitoring system for delivery of therapeutic gas |
US5497767A (en) * | 1993-02-05 | 1996-03-12 | Siemens Elema Ab | Method and apparatus for supplying fresh gas to a patient during manual ventilation |
US5503148A (en) * | 1994-11-01 | 1996-04-02 | Ohmeda Inc. | System for pulse oximetry SPO2 determination |
US5538002A (en) * | 1994-09-14 | 1996-07-23 | Boussignac; Georges | Device for respiratory assistance |
US5558086A (en) * | 1992-12-16 | 1996-09-24 | Freedom Air Services | Method and apparatus for the intermittent delivery of oxygen therapy to a person |
US5582164A (en) * | 1995-03-14 | 1996-12-10 | Stan A. Sanders | Cassette size, pressurized O2 coil structure |
US5603315A (en) * | 1995-08-14 | 1997-02-18 | Reliable Engineering | Multiple mode oxygen delivery system |
US5626131A (en) * | 1995-06-07 | 1997-05-06 | Salter Labs | Method for intermittent gas-insufflation |
US5664562A (en) * | 1992-09-18 | 1997-09-09 | Pierre Medical S.A. | Breathing aid device |
US5735268A (en) * | 1995-06-07 | 1998-04-07 | Salter Labs | Intermitten gas-insufflation apparatus and method therefor |
US5752509A (en) * | 1995-07-10 | 1998-05-19 | Burkhard Lachmann | Artificial ventilation system |
US5803066A (en) * | 1992-05-07 | 1998-09-08 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5810759A (en) * | 1997-03-27 | 1998-09-22 | Michigan Critical Care Consultants, Inc. | Control system for regulating gas exchange in extracoporeal circulation |
US5813399A (en) * | 1993-03-16 | 1998-09-29 | Puritan Bennett Corporation | System and method for closed loop airway pressure control during the inspiratory cycle of a breath in a patient ventilator using the exhalation valve as a microcomputer-controlled relief valve |
US5865174A (en) * | 1996-10-29 | 1999-02-02 | The Scott Fetzer Company | Supplemental oxygen delivery apparatus and method |
US5915381A (en) * | 1995-12-01 | 1999-06-29 | Siemens Elema Ab | Breathing apparatus and method for controlling same |
US5927274A (en) * | 1995-04-07 | 1999-07-27 | Healthdyne Technologies, Inc. | Pressure support ventilatory assist system |
US5931162A (en) * | 1996-06-03 | 1999-08-03 | Siemens Aktiengesellschaft | Ventilator which allows spontaneous inhalation and expiration within a controlled breathing mode |
US5934277A (en) * | 1991-09-03 | 1999-08-10 | Datex-Ohmeda, Inc. | System for pulse oximetry SpO2 determination |
US5937853A (en) * | 1995-11-16 | 1999-08-17 | Siemens Elema Ab | Ventilator for respiratory treatment |
US5954050A (en) * | 1997-10-20 | 1999-09-21 | Christopher; Kent L. | System for monitoring and treating sleep disorders using a transtracheal catheter |
US6041777A (en) * | 1995-12-01 | 2000-03-28 | Alliance Pharmaceutical Corp. | Methods and apparatus for closed-circuit ventilation therapy |
US6099481A (en) * | 1997-11-03 | 2000-08-08 | Ntc Technology, Inc. | Respiratory profile parameter determination method and apparatus |
US6142149A (en) * | 1997-10-23 | 2000-11-07 | Steen; Scot Kenneth | Oximetry device, open oxygen delivery system oximetry device and method of controlling oxygen saturation |
US6152134A (en) * | 1996-10-18 | 2000-11-28 | Invacare Corporation | Oxygen conserving device |
US6186142B1 (en) * | 1997-07-25 | 2001-02-13 | Minnesota Innovative Technologies & Instruments Corporation (Miti) | Control of respiratory oxygen delivery |
US6192883B1 (en) * | 1999-08-03 | 2001-02-27 | Richard L. Miller, Jr. | Oxygen flow control system and method |
US6220244B1 (en) * | 1998-09-15 | 2001-04-24 | Mclaughlin Patrick L. | Conserving device for use in oxygen delivery and therapy |
US6371114B1 (en) * | 1998-07-24 | 2002-04-16 | Minnesota Innovative Technologies & Instruments Corporation | Control device for supplying supplemental respiratory oxygen |
US6470885B1 (en) * | 2000-01-13 | 2002-10-29 | Brent Blue | Method and apparatus for providing and controlling oxygen supply |
US6532958B1 (en) * | 1997-07-25 | 2003-03-18 | Minnesota Innovative Technologies & Instruments Corporation | Automated control and conservation of supplemental respiratory oxygen |
Family Cites Families (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB336493A (en) * | 1928-12-10 | 1930-10-16 | Deutsch Englische Quarzschmelz | Improved process for and apparatus for use in moulding articles of fused quartz |
US5038770A (en) | 1989-02-03 | 1991-08-13 | Perkins Warren E | Fail-safe systems for respirating gas delivery devices |
DE4309923C2 (en) | 1993-03-26 | 1995-02-16 | Boesch Wilhelm | Device for supplying breathing gas to a patient |
US5697364A (en) | 1995-06-07 | 1997-12-16 | Salter Labs | Intermittent gas-insufflation apparatus |
US5692497A (en) * | 1996-05-16 | 1997-12-02 | Children's Medical Center Corporation | Microprocessor-controlled ventilator system and methods |
US5848591A (en) * | 1996-07-05 | 1998-12-15 | Dragerwerk Ag | Respirator with oxygen enrichment |
US6009481A (en) * | 1996-09-30 | 1999-12-28 | Emc Corporation | Mass storage system using internal system-level mirroring |
JP2001517108A (en) | 1997-01-17 | 2001-10-02 | メッサー オーストリア ゲゼルシャフト ミット ベシュレンクテル ハフツング | Controlled gas supply system |
US5925831A (en) * | 1997-10-18 | 1999-07-20 | Cardiopulmonary Technologies, Inc. | Respiratory air flow sensor |
-
1998
- 1998-07-24 US US09/463,614 patent/US6371114B1/en not_active Expired - Lifetime
-
2002
- 2002-02-14 US US10/076,001 patent/US6561187B2/en not_active Expired - Lifetime
-
2003
- 2003-02-20 US US10/370,799 patent/US7331343B2/en not_active Expired - Fee Related
- 2003-10-28 US US10/695,436 patent/US20040159323A1/en not_active Abandoned
-
2006
- 2006-05-26 US US11/441,525 patent/US20060213519A1/en not_active Abandoned
Patent Citations (99)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2414747A (en) * | 1942-07-02 | 1947-01-21 | Harry M Kirschbaum | Method and apparatus for controlling the oxygen content of the blood of living animals |
US2912979A (en) * | 1956-02-17 | 1959-11-17 | Lieber Samuel Loewenstein | Apparatus for administering and conserving gas |
US3400712A (en) * | 1965-08-12 | 1968-09-10 | James E. Finan | System for intermittently dispensing oxygen or other gas suitable for breathing |
US3400713A (en) * | 1966-10-12 | 1968-09-10 | James E. Finan | Apparatus for intermittently dispensing oxygen or other gas suitable for breathing |
US3493703A (en) * | 1968-08-02 | 1970-02-03 | James E Finan | Body motion sensitive electrical switch with lost motion means |
US3734091A (en) * | 1971-06-22 | 1973-05-22 | Airco Inc | Oxygen control system with blood oxygen saturation sensing means and method for closed system breathing |
US3834383A (en) * | 1972-12-11 | 1974-09-10 | Puritan Bennett Corp | Respiration apparatus with flow responsive control valve |
US4054133A (en) * | 1976-03-29 | 1977-10-18 | The Bendix Corporation | Control for a demand cannula |
US4336590A (en) * | 1979-05-02 | 1982-06-22 | Intertechnique | Devices for controlling gas flows |
US4326513A (en) * | 1979-07-02 | 1982-04-27 | Dragerwerk Ag | Patient data controlled respiration system |
US4278110A (en) * | 1979-11-13 | 1981-07-14 | Price Ernest H | Demand responsive flow controller |
US4457303A (en) * | 1980-11-26 | 1984-07-03 | Tritec Industries, Inc. | Respirating gas supply control method and apparatus therefor |
US4484578A (en) * | 1980-11-26 | 1984-11-27 | Kircaldie, Randall And Mcnab | Respirator apparatus and method |
US4381002A (en) * | 1980-12-18 | 1983-04-26 | The United States Of America As Represented By The Secretary Of The Army | Fluidic-controlled oxygen intermittent demand flow device |
US4648395A (en) * | 1982-07-07 | 1987-03-10 | Sanyo Densihkogyo Co. Ltd. | Synchronized feed type oxygen concentrator for use in an open breathing system |
US4567888A (en) * | 1982-07-13 | 1986-02-04 | Compagnie Francaise De Produits Oxygenes | Device for treating respiratory deficiency of a patient |
US4461293A (en) * | 1982-12-03 | 1984-07-24 | Kircaldie, Randall, And Mcnab | Respirating gas supply method and apparatus therefor |
US4506666A (en) * | 1982-12-03 | 1985-03-26 | Kircaldie, Randall And Mcnab | Method and apparatus for rectifying obstructive apnea |
US4519387A (en) * | 1982-12-03 | 1985-05-28 | Kircaldie, Randall And Mcnab, Trustee | Respirating gas supply method and apparatus therefor |
US4462398A (en) * | 1982-12-03 | 1984-07-31 | Kircaldie, Randal and McNab, Trustee | Respirating gas supply method and apparatus therefor |
US4665911A (en) * | 1983-11-25 | 1987-05-19 | Electro-Fluidics | Intermittent supplemental oxygen apparatus and method |
US4584996A (en) * | 1984-03-12 | 1986-04-29 | Blum Alvin S | Apparatus for conservative supplemental oxygen therapy |
US4575042A (en) * | 1984-08-17 | 1986-03-11 | Associates Of Dallas | Pneumatically amplified conservation valve |
US4612928A (en) * | 1984-08-28 | 1986-09-23 | Tiep Brian L | Method and apparatus for supplying a gas to a body |
US4681099A (en) * | 1984-11-30 | 1987-07-21 | Tottori University | Breath-synchronized concentrated-oxygen supplier |
US4686975A (en) * | 1985-05-03 | 1987-08-18 | Applied Membrane Technology, Inc. | Electronic respirable gas delivery device |
US4705034A (en) * | 1985-10-02 | 1987-11-10 | Perkins Warren E | Method and means for dispensing respirating gases by effecting a known displacement |
US5005570A (en) * | 1985-10-02 | 1991-04-09 | Perkins Warren E | Method and means for dispensing respirating gases by effecting a known displacement |
US4873971A (en) * | 1985-10-02 | 1989-10-17 | Perkins Warren E | Method and means for dispensing respirating gases by effecting a known displacement |
US4686974A (en) * | 1985-10-18 | 1987-08-18 | Tottori University | Breath synchronized gas-insufflation device and method therefor |
US5052400A (en) * | 1986-02-20 | 1991-10-01 | Dietz Henry G | Method and apparatus for using an inhalation sensor for monitoring and for inhalation therapy |
US4744356A (en) * | 1986-03-03 | 1988-05-17 | Greenwood Eugene C | Demand oxygen supply device |
US4706664A (en) * | 1986-04-11 | 1987-11-17 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US4932402A (en) * | 1986-04-11 | 1990-06-12 | Puritan-Bennett Corporation | Inspiration oxygen saver |
US4745925A (en) * | 1986-10-06 | 1988-05-24 | Dietz Henry G | Optoelectronic inhalation sensor for monitoring inhalation and for inhalation therapy |
US4784130A (en) * | 1986-12-04 | 1988-11-15 | The John Bunn Company | Flow controller |
US5024219A (en) * | 1987-01-12 | 1991-06-18 | Dietz Henry G | Apparatus for inhalation therapy using triggered dose oxygenator employing an optoelectronic inhalation sensor |
US4827922A (en) * | 1987-03-05 | 1989-05-09 | L'air Liquide | Process and device for supplying respiratory oxygen |
US5360000A (en) * | 1987-03-19 | 1994-11-01 | Puritan-Bennett Corporation | Pneumatic demand oxygen valve |
US4889116A (en) * | 1987-11-17 | 1989-12-26 | Phospho Energetics, Inc. | Adaptive control of neonatal fractional inspired oxygen |
US4883353A (en) * | 1988-02-11 | 1989-11-28 | Puritan-Bennett Corporation | Pulse oximeter |
US4823788A (en) * | 1988-04-18 | 1989-04-25 | Smith Richard F M | Demand oxygen controller and respiratory monitor |
US5103814A (en) * | 1988-04-28 | 1992-04-14 | Timothy Maher | Self-compensating patient respirator |
US5074299A (en) * | 1988-05-02 | 1991-12-24 | Dietz Henry G | Monitor for controlling the flow of gases for breathing during inhalation |
US4972842A (en) * | 1988-06-09 | 1990-11-27 | Vital Signals, Inc. | Method and apparatus for precision monitoring of infants on assisted ventilation |
US5048515A (en) * | 1988-11-15 | 1991-09-17 | Sanso David W | Respiratory gas supply apparatus and method |
US5165397A (en) * | 1988-12-15 | 1992-11-24 | Arp Leon J | Method and apparatus for demand oxygen system monitoring and control |
US5137017A (en) * | 1989-04-13 | 1992-08-11 | Salter Labs | Demand oxygen system |
US4971049A (en) * | 1989-11-06 | 1990-11-20 | Pulsair, Inc. | Pressure sensor control device for supplying oxygen |
US5038771A (en) * | 1990-01-25 | 1991-08-13 | Dietz Henry G | Method and apparatus for respiratory therapy using intermittent flow having automatic adjustment of a dose of therapeutic gas to the rate of breathing |
US5099837A (en) * | 1990-09-28 | 1992-03-31 | Russel Sr Larry L | Inhalation-based control of medical gas |
US5251632A (en) * | 1991-03-07 | 1993-10-12 | Hamamatsu Photonics K.K. | Tissue oxygen measuring system |
US5365922A (en) * | 1991-03-19 | 1994-11-22 | Brigham And Women's Hospital, Inc. | Closed-loop non-invasive oxygen saturation control system |
US5934277A (en) * | 1991-09-03 | 1999-08-10 | Datex-Ohmeda, Inc. | System for pulse oximetry SpO2 determination |
US5315990A (en) * | 1991-12-30 | 1994-05-31 | Mondry Adolph J | Method for delivering incremental doses of oxygen for maximizing blood oxygen saturation levels |
US5490502A (en) * | 1992-05-07 | 1996-02-13 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5546933A (en) * | 1992-05-07 | 1996-08-20 | New York University | Method for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5803066A (en) * | 1992-05-07 | 1998-09-08 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5535739A (en) * | 1992-05-07 | 1996-07-16 | New York University | Method and apparatus for optimizing the continuous positive airway pressure for treating obstructive sleep apnea |
US5282464A (en) * | 1992-07-21 | 1994-02-01 | Brain Archibald Ian Jeremy | Combined laryngeal mask and reflectance oximeter |
US5398682A (en) * | 1992-08-19 | 1995-03-21 | Lynn; Lawrence A. | Method and apparatus for the diagnosis of sleep apnea utilizing a single interface with a human body part |
US5664562A (en) * | 1992-09-18 | 1997-09-09 | Pierre Medical S.A. | Breathing aid device |
US5388575A (en) * | 1992-09-25 | 1995-02-14 | Taube; John C. | Adaptive controller for automatic ventilators |
US5323776A (en) * | 1992-10-15 | 1994-06-28 | Picker International, Inc. | MRI compatible pulse oximetry system |
US5280780A (en) * | 1992-11-09 | 1994-01-25 | Abel Elaine R | Oxygen delivery and conserving device |
US5558086A (en) * | 1992-12-16 | 1996-09-24 | Freedom Air Services | Method and apparatus for the intermittent delivery of oxygen therapy to a person |
US5438980A (en) * | 1993-01-12 | 1995-08-08 | Puritan-Bennett Corporation | Inhalation/exhalation respiratory phase detection circuit |
US5497767A (en) * | 1993-02-05 | 1996-03-12 | Siemens Elema Ab | Method and apparatus for supplying fresh gas to a patient during manual ventilation |
US5813399A (en) * | 1993-03-16 | 1998-09-29 | Puritan Bennett Corporation | System and method for closed loop airway pressure control during the inspiratory cycle of a breath in a patient ventilator using the exhalation valve as a microcomputer-controlled relief valve |
US5398676A (en) * | 1993-09-30 | 1995-03-21 | Press; Roman J. | Portable emergency respirator |
US5443062A (en) * | 1993-11-23 | 1995-08-22 | Hayes; Jeffrey P. | Load activated oxygen delivery system |
US5429123A (en) * | 1993-12-15 | 1995-07-04 | Temple University - Of The Commonwealth System Of Higher Education | Process control and apparatus for ventilation procedures with helium and oxygen mixtures |
US5538002A (en) * | 1994-09-14 | 1996-07-23 | Boussignac; Georges | Device for respiratory assistance |
US5503148A (en) * | 1994-11-01 | 1996-04-02 | Ohmeda Inc. | System for pulse oximetry SPO2 determination |
US5495848A (en) * | 1994-11-25 | 1996-03-05 | Nellcar Puritan Bennett | Monitoring system for delivery of therapeutic gas |
US5582164A (en) * | 1995-03-14 | 1996-12-10 | Stan A. Sanders | Cassette size, pressurized O2 coil structure |
US5927274A (en) * | 1995-04-07 | 1999-07-27 | Healthdyne Technologies, Inc. | Pressure support ventilatory assist system |
US5626131A (en) * | 1995-06-07 | 1997-05-06 | Salter Labs | Method for intermittent gas-insufflation |
US5735268A (en) * | 1995-06-07 | 1998-04-07 | Salter Labs | Intermitten gas-insufflation apparatus and method therefor |
US5752509A (en) * | 1995-07-10 | 1998-05-19 | Burkhard Lachmann | Artificial ventilation system |
US5603315A (en) * | 1995-08-14 | 1997-02-18 | Reliable Engineering | Multiple mode oxygen delivery system |
US5937853A (en) * | 1995-11-16 | 1999-08-17 | Siemens Elema Ab | Ventilator for respiratory treatment |
US6041777A (en) * | 1995-12-01 | 2000-03-28 | Alliance Pharmaceutical Corp. | Methods and apparatus for closed-circuit ventilation therapy |
US5915381A (en) * | 1995-12-01 | 1999-06-29 | Siemens Elema Ab | Breathing apparatus and method for controlling same |
US5931162A (en) * | 1996-06-03 | 1999-08-03 | Siemens Aktiengesellschaft | Ventilator which allows spontaneous inhalation and expiration within a controlled breathing mode |
US6152134A (en) * | 1996-10-18 | 2000-11-28 | Invacare Corporation | Oxygen conserving device |
US5865174A (en) * | 1996-10-29 | 1999-02-02 | The Scott Fetzer Company | Supplemental oxygen delivery apparatus and method |
US5810759A (en) * | 1997-03-27 | 1998-09-22 | Michigan Critical Care Consultants, Inc. | Control system for regulating gas exchange in extracoporeal circulation |
US6532958B1 (en) * | 1997-07-25 | 2003-03-18 | Minnesota Innovative Technologies & Instruments Corporation | Automated control and conservation of supplemental respiratory oxygen |
US6186142B1 (en) * | 1997-07-25 | 2001-02-13 | Minnesota Innovative Technologies & Instruments Corporation (Miti) | Control of respiratory oxygen delivery |
US20030145852A1 (en) * | 1997-07-25 | 2003-08-07 | Minnesota Innovative Technologies And Instruments | Control of supplemental respiratory Oxygen |
US6561187B2 (en) * | 1997-07-25 | 2003-05-13 | Minnesota Innovative Technologies & Instruments Corporation | Control of supplemental respiratory oxygen |
US5954050A (en) * | 1997-10-20 | 1999-09-21 | Christopher; Kent L. | System for monitoring and treating sleep disorders using a transtracheal catheter |
US6142149A (en) * | 1997-10-23 | 2000-11-07 | Steen; Scot Kenneth | Oximetry device, open oxygen delivery system oximetry device and method of controlling oxygen saturation |
US6099481A (en) * | 1997-11-03 | 2000-08-08 | Ntc Technology, Inc. | Respiratory profile parameter determination method and apparatus |
US6371114B1 (en) * | 1998-07-24 | 2002-04-16 | Minnesota Innovative Technologies & Instruments Corporation | Control device for supplying supplemental respiratory oxygen |
US6220244B1 (en) * | 1998-09-15 | 2001-04-24 | Mclaughlin Patrick L. | Conserving device for use in oxygen delivery and therapy |
US6192883B1 (en) * | 1999-08-03 | 2001-02-27 | Richard L. Miller, Jr. | Oxygen flow control system and method |
US6470885B1 (en) * | 2000-01-13 | 2002-10-29 | Brent Blue | Method and apparatus for providing and controlling oxygen supply |
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Also Published As
Publication number | Publication date |
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US6371114B1 (en) | 2002-04-16 |
US20020112726A1 (en) | 2002-08-22 |
US7331343B2 (en) | 2008-02-19 |
US6561187B2 (en) | 2003-05-13 |
US20030145852A1 (en) | 2003-08-07 |
US20040159323A1 (en) | 2004-08-19 |
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