WO2002070734A1 - Method for determining concentration of an analyte in a test strip - Google Patents
Method for determining concentration of an analyte in a test strip Download PDFInfo
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- WO2002070734A1 WO2002070734A1 PCT/US2002/003415 US0203415W WO02070734A1 WO 2002070734 A1 WO2002070734 A1 WO 2002070734A1 US 0203415 W US0203415 W US 0203415W WO 02070734 A1 WO02070734 A1 WO 02070734A1
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- WIPO (PCT)
- Prior art keywords
- measuring
- fluid sample
- value
- analyte
- final
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Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N33/00—Investigating or analysing materials by specific methods not covered by groups G01N1/00 - G01N31/00
- G01N33/48—Biological material, e.g. blood, urine; Haemocytometers
- G01N33/50—Chemical analysis of biological material, e.g. blood, urine; Testing involving biospecific ligand binding methods; Immunological testing
- G01N33/53—Immunoassay; Biospecific binding assay; Materials therefor
- G01N33/543—Immunoassay; Biospecific binding assay; Materials therefor with an insoluble carrier for immobilising immunochemicals
- G01N33/54366—Apparatus specially adapted for solid-phase testing
- G01N33/54386—Analytical elements
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/84—Systems specially adapted for particular applications
- G01N21/8483—Investigating reagent band
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T436/00—Chemistry: analytical and immunological testing
- Y10T436/14—Heterocyclic carbon compound [i.e., O, S, N, Se, Te, as only ring hetero atom]
- Y10T436/142222—Hetero-O [e.g., ascorbic acid, etc.]
- Y10T436/143333—Saccharide [e.g., DNA, etc.]
- Y10T436/144444—Glucose
Definitions
- the present invention relates generally to methods of measuring the concentration of an analyte in a fluid sample. More particularly, this invention provides i methods for determining the appropriate point at which to take a measurement of an analyte concentration in a fluid sample applied to a test strip.
- analytes such as glucose, cholesterol, intoxicants, and other constituents is frequently desirable in fluids, such as blood, plasma, blood serum, saliva,
- Diabetics suffer from an impaired ability to regulate glucose levels in their blood.
- diabetics can have abnormally high blood sugar levels known as hyperglycemia.
- Chronic hyperglycemia may lead to long-term complications such as cardiovascular disease and degeneration of the kidneys, retinas, blood vessels and the nervous system.
- diabetics must strictly monitor and manage their blood
- Reflectance based monitors comprise one category of personal, or home-use, glucose level monitoring devices. These monitors utilize an optical block which accepts test elements for photometric analysis.
- test elements are usually in the form of test strips, which contain analytical chemistry.
- these test strips are in the form of a disposable diagnostic test strip containing analytical chemistry upon which a fluid sample is deposited.
- a chemical reaction occurs in the presence of a target analyte, e.g., glucose, to cause a change in the optical properties of the test strip.
- An optical photometric device determines the analyte level of the sample by measuring an optical property, such as the intensity of reflected light at a certain wavelength from the test strip.
- the fluid sample is usually fresh whole blood.
- test strips for testing analytes such as glucose levels of blood samples are well known in the art and comprise various structures and materials. Test strips typically include single or multi-layered porous membrane arrangements which receive a blood sample and undergo a change in an optical property, such as a color change, in response to the interaction of blood glucose with agents/reactants in the membrane. Examples of such multi-layer strips are described in U.S. Patents 5,296,192 to Carroll and 6,010,999 to Carroll et al., the contents of both of which are incorporated herein by reference.
- a whole blood sample Prior to reaching the reactants, a whole blood sample can be filtered to eliminate potential optical interference by removing erythrocytes, or red blood cells.
- Some test strips operate to allow the applied blood sample to migrate to a reaction site in the membrane where the sample reacts with the agents/reactants, which is located in downstream capillary relation to the sample application site.
- the results of the reaction are often visible as a color change at the reaction site.
- the change may occur in invisible regions of the electromagnetic spectrum, such as infrared and ultraviolet.
- the term "color change" will be understood to include variations in optical properties throughout the visible and invisible regions of the electromagnetic spectrum. As noted above, a color change can be correlated to the amount of glucose in the sample.
- Home-use glucose measuring devices that use a reflectance meter to measure the color change of the test strip correlate glucose levels to the change in the amount of light reflected from the reaction site of the test strip.
- strips can be formulated to produce a color change within a certain spectral region, and the meter designed to photometrically measure reflected, absorbed or transmitted light at a wavelength sensitive to the color change of the strip. While the present invention will be described with reference to reflectance based photometry, it would be known to one having ordinary skill in the art to apply the features of the invention to absorbance or transmittance based systems.
- An important aspect to the accurate measurement of glucose levels in a fluid using a test strip are the methods used to calculate the glucose concentration values from the reflectance values obtained. Because different samples physically vary and will contain different levels of analyte, reaction rates and durations will vary. Prior art devices have focused on fixing an initiation point, the time from which the monitoring device begins to measure the chemical reaction of the blood sample with the test strip. This initiation point often was carefully tied to the initial contact of analyte and reagent, either manually or automatically and then the reaction was timed for a fixed period of time from this initiation point. The end point is the time at which the monitoring device takes a final reflectance reading to calculate the reported glucose level of the sample from calibration data stored in the meter's memory.
- Some home-use glucose monitoring devices have an initiation point corresponding to manual, or user determined events. For example, some monitoring devices trigger the initiation point for measuring glucose levels upon the pressing of a button, the insertion of a test strip into the monitoring device, or upon closing an element, such as a cover or door, of the monitoring device over the test strip. These user-defined initiation points decrease the accuracy and consistency of the monitoring device because they rely on the inconsistent timing of an action by the user (i.e. insertion or covering of the test strip in the monitoring device).
- a method for measuring an analyte in a fluid sample in a meter system comprising the steps of: a) initiating a measuring period for a fluid sample; b) measuring a property of the fluid sample at each of n points in time, said multiple points in time being spaced at predetermined intervals to form a sequence of n measurement values, where n is an integer; c) comparing two nonconsecutive measurement values to determine at least one ratio; d) terminating the measuring of the fluid sample when at least one of said at least one ratio meets predetermined criteria indicating a final analyte value can be accurately determined; and e) determining a final analyte value based on said measurement values.
- a meter system for measuring an analyte in a fluid sample, comprising: a light intensity control circuit for measuring reflectance values of an analytic test strip onto which a fluid sample has been applied; and a processor for (a) initiating a measuring period for a fluid sample; (b) measuring the reflectance of a portion of the test strip onto which the fluid sample has been applied at each of n points in time, said multiple points in time being spaced at predetermined intervals to form a sequence of n calculated measurement values, where n is an integer; (c) comparing two nonconsecutive measurement values to determine at least one ratio; (d) terminating the reflectance measuring when at least one of said at least one ratio meets predetermined criteria indicating a final analyte value can be accurately determined; and (e) determining a final analyte value based on said measurement values; and a display for reporting said final analyte value in a user comprehensible format.
- Fig. 1 is a perspective view of an analyte meter system according to an illustrative embodiment of the present invention
- Fig. 2 is a test strip for receiving test fluid according to an illustrative embodiment of the present invention
- Fig. 3 illustrates a blood test subroutine of the meter system of Fig. 1
- Fig. 4 illustrates a representative graph of Glucose v. Time resulting from the blood test subroutine of Fig. 3;
- Fig. 5 is a schematic representation of a meter system according to the present invention.
- Fig. 1 depicts an analyte meter system 10 according to the present invention.
- Meter system 10 generally includes a hand-held meter having a housing enclosure 12, power switch/button 14, up/down menu navigation button 15, menu select button 17, liquid crystal display (LCD) 18, and removable test chamber cover or shroud 16 having a test strip platform 20 for receiving and testing a multi-layered diagnostic test strip 40 for the amount of a suspected analyte, such as glucose, cholesterol, ketones, theophylline, fructosamine, and others.
- a strip sensor (not shown) of known configuration is located at a distal end of the strip platform 20 to detect when a test strip 40 has been fully inserted into the device.
- Fig. 2 illustrates an enlarged view of a representative diagnostic test strip 40.
- Test strip 40 generally includes an upper and lower support layer 41 , 42, with sample receiving layers 50 located between the support layers.
- Sample receiving layers 50 include a spreading layer 47 located adjacent upper support layer 41 , a separating layer 48, and a semi-porous membrane reagent layer 49 located adjacent lower support layer 42.
- At least one of the sample receiving layers 50 is pretreated with a dry chemistry reagent and conditioning solution.
- the membrane 49 and separating layer 48 are pretreated with the reagent/conditioning solution.
- the spreading layer 47 may also be treated.
- Each layer is positioned in substantially continuous contact with its adjacent layer as shown in Fig. 2 by adhesives and ultrasonic bonding or other known means to provide a sealed composite structure.
- the top and bottom support layers 41 , 42 of test strip 40 each define an aperture or opening therethrough. These apertures or openings of the test strip are oriented in vertical alignment with test window of the meter (not shown) located along the strip platform, when properly positioned in meter system 10.
- the opening in the upper support strip 41 defines a sample receiving port 44a and the opening in the lower support strip defines a reaction viewing port 44b.
- the sample receiving layers 50 are oriented in vertical alignment with sample receiving port 44a and reaction viewing port 44b. This allows the blood sample received by the strip to pass directly from receiving port 44a to viewing port 44b.
- test strip of Fig. 2 is illustrative only and many other test strip configurations may be used when practicing the present invention.
- Monitoring meter system 10 of the present invention includes a circuit assembly physically and electrically connected to a printed circuit board, an example of which is schematically depicted as the block diagram of Fig. 5.
- the circuit 100 contains a microprocessor 102 with a plurality of inputs and outputs.
- An exemplary embodiment of the present invention uses an 8-bit device with 60K of programmable memory.
- the microprocessor executes the meter instruction code.
- the microprocessor receives input from the user through input device 104, which can include buttons or other input devices known in the art.
- a display 106 and a sounder 107 or similar output devices receives data from the microprocessor for presentation to the user.
- a memory device 108 for example EEPROM, is also connected for input from and output to the microprocessor 102.
- a communication port 110 can also connected in input-output relationship with the microprocessor in known manner.
- a strip sensor 112 receives a drive signal through line 114 to turn on and off photo element 116.
- the photo element can be an LED.
- Light from the photo element 116 is detected by the photodetector 118.
- the photodetector can be a photodiode or phototransistor. Output from the photodetector is supplied via line 120 to the microprocessor 102.
- the strip sensor detects when a test strip is inserted into the meter, and can be initialized by the method described in commonly assigned, copending US Patent Application 09/ , (Atty Docket 0043-00000 entitled
- the circuit assembly can include a light intensity control circuit, represented as section 122 of the diagram, and a light detector circuit 124, discussed in further detail hereinbelow.
- An exemplary embodiment of the present invention operates using a DC offset ("virtual ground") of 2.5V reference (not shown) and is powered from a 1.5V AAA battery (not shown), which may include a voltage divider circuit or other power management circuitry as is known in the art.
- An analog to digital (AID) converter 126 converts analog electrical output on line 128 from the light detector circuit 124 into digital information for the microprocessor 102.
- AID analog to digital
- a temperature sensor 130 provides a voltage proportional to the temperature along line 132 to the A/D converter.
- the microprocessor 102 can make a determination as to whether the temperature of the testing environment is within predetermined thresholds, and prohibit a user from running a test if accuracy would be negatively affected.
- the light intensity control circuit (LICC) 122 will now be described.
- the circuit is supplied by a pulse width modulated signal along line 134 from the microprocessor 102.
- the circuit includes a low pass filter 136, a modulator 137, a flux biasing resistor 138, a reference photodiode 140, a control loop error amplifier 142, a feedback loop compensation capacitor 144, and LED drive transistors 146.
- the LICC controls the drive supplied to the LEDs 148, as will be described.
- the LEDs generate light, a component 150 of which will encounter the target 152, which is the test strip or other test element inserted into the meter. Another component 154 of the light strikes a chamber reflector 156 and a portion of which 158 is reflected toward reference photodiode 140.
- One of the LEDs is a 660nm LED in the exemplary embodiment, which is appropriate for detecting glucose in a test strip marketed under the tradename PRESTIGE and sold by Home Diagnostics, Inc. of Ft. Lauderdale, FL.
- the exemplary embodiment can be easily modified for detecting other analytes or using other strips by changing the software and LED used to obtain a different wavelength. For instance, a 580nm LED would be preferred for ketones using known analytical chemistry systems.
- the LDC includes a main photodiode 160, a transimpedance (current to voltage) amplifier 162, a high pass filter 164, an amplifier 166, and a negative gain amplifier 168.
- the output stage of the exemplary LDC includes a demodulator 170, a level shifting amplifier 172, and a low pass filter 174.
- the output stage provides a DC voltage to line 128, as set forth above.
- the LDC supplies an analog signal to the A/D converter, which when digitized is interpreted by the microprocessor to provide test results.
- input to the A/D converter is conventionally multiplexed, receiving input from lines 128 and 132, and from other signal lines not shown and not necessary to understand the present invention.
- two LEDs are employed, at 610 nm and 660 nm as described herein.
- the LEDs are selected according to the instruction code at appropriate times by the microprocessor 102 by a signal sent via line 176, which activates a switch 178. If additional LEDs are employed, then additional signal lines and switches can be added in conventional manner. The selection between the two LEDs in the exemplary embodiment is the subject of commonly assigned copending US
- Patent Application 09/ (Atty Docket 0008-00000 entitled "Distinguishing Test
- a pulse width signal is produced by the microprocessor 102 along line 134.
- the pulse width modulation signal is basically a 2.5V signal delivered either on or off according to a duty cycle.
- the duty cycle is 50%, so that the signal is 50% on, and 50% off. Accordingly, when the signal is on, it is delivered at 2.5 volts and when it's off, it is zero volts.
- the signal in line 134 is averaged by the low pass filter 136 to arrive at a drive voltage for the LEDs, which will in turn determine their output. For example, for a perfect 2.5V square wave, the average voltage, and thus the output of the low pass filter 136 will be 1.25V. In this way, the power delivered to the LEDs can be modified by the microprocessor by changing the duty cycle of the pulse width modulation signal. To increase the light power, the duty cycle of the signal would be increased.
- the duty cycle of the pulse width modulation signal is determined during factory calibration of the meter, and the duty cycle value is permanently stored in the EEPROM.
- periodic calibration routines known in the art could also be employed.
- different LEDs may have different preferred drive requirements, so different duty cycles can be utilized based on the LED in operation.
- the circuit 100 employes a modulation or "chopping" function controlled by the microprocessor 102.
- the microprocessor 102 supplies a modulation signal via line 180 to the modulator 137 of the LICC and to the demodulator 170 of the LDC in synchrony.
- the chopping signal is essentially a square wave (on/off) signal supplied to drive the LEDs at a certain frequency, rather than at constant power, to eliminate noise in the signal output of the circuit. In the exemplary embodiment, a 2 kHz chop is employed.
- the chopping function allows the shifting of the frequency of the light signals LICC upward to a "quieter" region of the spectrum where ambient light effects can be minimized in the LDC.
- incandescent lights have a frequency of 120 Hz. Fluorescent lights are also 120 Hz, but also have harmonic frequencies. By shifting the drive frequency of the LEDs above that of ambient light at the LICC, the LDC will be able to receive a signal at the matching frequency that is above the spectrum where most noise is encountered.
- the LICC includes flux biasing resistor 138 which is in parallel with modulator 137.
- This resistor in parallel essentially inhibits the voltage from the low pass filter 136 from being completely turned off by the modulator 137.
- the chopping function instead of modulating between full-on to full-off will modulate between full-on and low.
- the LEDs will be either full-on or dim, but never completely off.
- This positive bias helps to compensate for this tendency toward ground and allows the circuit to adapt without a change in peak-to-peak amplitude by keeping the modulated signal above ground.
- the control loop amplifier 142 in connection with the compensation capacitor 144 receives the output from the reference photodiode 140 to provide a feedback mechanism in determining the appropriate drive power for the LEDs 148.
- reflected light 153 is received by the main photodiode 160, producing a photocurrent based on the reflectance.
- the photocurrent output of the photodiode 160 is supplied to transimpedance amplifier 162, which converts the photocurrent to a voltage.
- This voltage is conditioned by high pass filter 164, which removes noise components of the signal below the chopping frequency. It is here that the noise components of artificial lighting are filtered out, although certain harmonics of fluorescent light are eliminated after demodulation by low pass filter 174.
- a 400 Hz cutoff frequency is employed in high pass filter 164.
- the signal emerging from high pass filter 164 is basically a square wave voltage at the chopping frequency that is nominally .5V peak-peak maximum and centered about the vitual ground of 2.5V.
- amplifier 166 and negative gain amplifier 168 are employed as follows. When the LED is on, the top half of the square wave is connected by level shifting amplifier 172; and when the LED is off, the bottom half of the square wave is amplified by minus unity and connected by level shifting amplifier 172. This inverts the bottom half of the square wave when the LED is off.
- the demodulator 170 selects between the amplifiers 166, 168 in synchrony with the modulation occurring in the LIDC at modulator 137.
- the resulting signal emerging from demodulator 170 is a DC signal proportional to the reflectance of the chemistry, in relation to the 2.5V reference voltage in the exemplary embodiment.
- Level shifting amplifier 172 receives the DC signal from the demodulator 170, applies a gain and shifts the signal to a range acceptable to the A/D converter, which in the exemplary embodiment is approximately 2.6V maximum.
- Low pass filter 174 removes spiking introduced by the demodulation of the signal by amplifiers 166, 168, and also removes a large amount of the harmonics of artificial light that were shifted high by the demodulation. Further, Any DC offsets in the amplifier stages prior to the demodulations that were shifted up to the chopping frequency are also effectively filtered. The only noise left in the signal are harmonics of ambient light that are right around the chopping frequency, which in the exemplary embodiment of 2 kHz are minimal.
- the chop frequency is 2048 HZ, which is more conveniently generated by binary digital systems than 2000Hz, the strongest remaining interfering harmonic will be 8 Hz (
- ). Since this interfering signal is of known frequency, it can be further reduced by simple synchronous digital filtering techniques. In countries that use 50Hz power grids, the strongest interfering frequency will be 2 Hz (the 25 th harmonic of 100Hz 2050Hz,
- 2Hz). A simple synchronous digital filtering technique that "nulls- out" both 2Hz and 8Hz can be implemented.
- the microprocessor and code of instructions perform the calculations to arrive at the ultimate reported glucose measurement. It should be noted, however, that similar calculations can be used for deriving the amount of other analytes found in the fluid sample applied to the test strip so long as meter system 10 has been properly configured and calibrated for the particular test (analyte/reagent pair, etc.) of interest.
- the equations used for determining the glucose level calculations derived from Kubelka-Munk, are listed below. The first calculation is the K/S calculation and is as follows:
- the K/S value which compares light absorbed to light scattered, is directly related to the percentage of reflectance (R) measured by the light detector(s) as calculated by the microprocessor.
- the K/S calculation is then used to determine the glucose value in a linear equation.
- the glucose calculation is determined as follows:
- the instruction code includes a plurality of routines for operating meter system 10.
- the aspects of meter software include but are not limited to: meter power-up, system diagnostics, meter readying, meter calibration, reflectance and optics calibration, code curve calibration, strip sensor calibration, temperature calibration, the blood test algorithm, test strip code management, test results storage and recall, standard strip test management, operational mode management, and user preferences setup.
- the operational aspects of the software discussed above can be in any conventional format.
- the blood test algorithm discussed below is initiated immediately upon the insertion of a test strip upon which fluid containing the analyte of interest has already been placed, and a reaction already underway.
- the insertion of a test strip 40 into the platform 20 trips a strip sensor 112 as shown in Fig. 5 which comprises a phototransistor or photodiode that initiates the blood test algorithm.
- the strip insertion can be detected as described in commonly assigned copending patent application
- the blood test algorithm is illustrated in Fig. 3 and includes steps 100 through 138.
- the code curve parameters are obtained at step 102.
- the code curves are calibration values stored in the memory of the device to account for slight lot-to-lot variations that occur due to strip manufacturing and processing.
- the subroutine then provides a check to determine whether a period of time, for example 80 seconds, have elapsed without completing the blood test procedure and arriving at a final value for glucose, or whether the strip has been removed from test strip platform, or shroud 20. If this termination period of e.g. 80 seconds has elapsed, or the test strip has been removed, an error is indicated and the meter system powers down (steps 104-108 of Fig. 3).
- the next step in the blood test algorithm includes performing an intermediate glucose reading and saving the results thereof in an intermediate glucose buffer (110, 112).
- the subroutine determines whether 6 or more glucose reading have occurred (114). If 6 readings have not occurred, the system waits the remainder of one second from the previous reading and checks again whether the termination period has expired, and whether the strip is still in the shroud 20 (steps 116, 104, 108). If the termination period has not elapsed and the test strip is still in place, a second reading of the test strip is performed and the glucose intermediate value is calculated and stored. This sequence continues until six or more readings are stored in the intermediate glucose buffer. These intermediate glucose values are values obtained by the glucose calculation, but may not represent the actual glucose concentration of the sample if the reaction has not stabilized.
- a ratio of the sixth glucose value to the first glucose value is calculated at step 118. If this ratio is greater than 1.025, then another, seventh glucose value is obtained as set forth in steps 104-116 described above (120, 122). With the seventh glucose value obtained, a ratio of the seventh glucose value to the second glucose value is calculated. If again the ratio is greater than 1.025, then another, eighth glucose value is measured. This process continues with the glucose measurements taken at periodic intervals, and a ratio of the (n) lh to the (n-5) th reading is calculated after each glucose value is determined, where "n" corresponds to the number of readings that have taken place.
- measurements can be taken at one second intervals, thus, "n" can correspond to both the number of measurements and, after the sixth measurement is taken, the number of seconds since insertion of an already reacted strip into the meter system.
- the successive ratio calculations are illustrated in the Glucose v. Time graph of Fig. 4. On the graph, time is depicted on the x-axis with values from glucose in mg/dl reported on the y-axis. Representative glucose values beginning 20 seconds after the insertion of an already reacting strip into the meter system are depicted.
- a ratio is calculated comparing the value obtained for glucose, or 258 mg/dL, to the value obtained at (25 - 5), or 20 seconds, which is 249 mg/dL.
- the calculated ratio of these two glucose values is 1.036.
- the ratio of the glucose value obtained at 31 seconds as compared to at (31 - 5), or 26 seconds is equal to 1.019, which is less than 1.025.
- the next ratio calculated (at 27 seconds), as seen across the top border of the graph is 1.027.
- Two consecutive ratios must be calculated as being less than 1.025 in order for the meter to report a final glucose value.
- the calculated ratio is less than 1.025, resulting from the comparison at the glucose value obtained at 34 seconds to that obtained at (34 - 5), or 29 seconds, resulting in a ratio of 1.023.
- the next calculated ratio, at arrow "C”, is 1.023, satisfying the condition that two consecutive calculated ratios are less than 1.025.
- the final value for glucose calculated by the meter can be that obtained at arrow C, at 35 seconds, or 271 mg/dL.
- the glucose testing end point is presumed to have been reached and the testing is deemed complete.
- the final calculated glucose value is then converted to the appropriate units and reference type and displayed on the LCD (steps 130, 138).
- the final calculated glucose value is the value calculated at time (n) of the second ratio that was calculated to be less than or equal to 1.025. A long, audible beep can be sounded and the final glucose value displayed, or further processing may occur as discussed below.
- meter system 10 can check if battery voltage is sufficient, and can check if the ambient light is acceptable (steps 132, 134). If ambient light levels are not acceptable at either the reflectance or the reference detector, an error message can be displayed, and the final glucose reading is not displayed and the system is powered down (134). These tests can be performed initially or periodically and need not be performed only at the end of the test.
- the final glucose value displayed to the user can be obtained by averaging the second glucose values (n) from each of the ratios found to be less than or equal to the value of 1.025.
- the value reported to the user can be calculated from an extrapolation into the future based on the slope of line connecting the two final glucose values averaged in the previous example.
- the slope connecting the readings of 270 and 271 mg/dL, or 1 mg/dL/s can be used to extrapolate glucose values into the future. Because the ratio condition of 1.025 is met two consecutive times, the reaction kinetics have practically slowed nearly to the actual theoretical end point of the reaction, and the slope of this predictive line will be relatively flat. Prediction into the future using the glucose values at arrows B and C can be employed to accurately extrapolate a final reported measurement without having to wait for reflectance measurements to be taken.
- a negative slope can also indicate that a fully reacted test strip has been inserted, and the decreasing glucose values calculated by the algorithm after full reaction could be the result of various phenomena, for example by the formation of late reaction products.
- managing negative slope conditions allows the meter in accordance with the present invention to exclude from testing fully reacted test strips, and avoids reporting potentially erroneous results to the user.
- the meter can signal an error condition and abort the test. If negative slope is not persistently observed and only occurs at the very end of the testing period, a negative slope can be avoided by correcting the condition contributing to the negative slope before any extrapolation.
- the meter can predict for a zero slope in these instances, in which case the extrapolated value would be equal to the final calculated glucose value.
- Other techniques can also be employed. For linear extrapolation, two sequential calculated glucose values used in the extrapolation can be averaged to arrive at a positive or zero slope, or the value statistically determined in a known manner to be most likely in error excluded. The second derivative of the calculated glucose values can also be employed.
- monitoring meter system 10 may include a memory for storing successive final glucose values.
- the memory may hold a collection of successive final glucose values, such as, for example, 365 values. With the capacity of modern subminiature memory chips, a very large amount of data can be reliably stored. These final values can be recalled by pressing a control button 15.
- meter system 10 may include a data port or a modem assembly for downloading the stored final glucose values to another computer system.
- the computer system receiving the downloaded final glucose values could be a home PC, or that of a doctor, or a website operator, or any other person or organization for providing assistance to the user in monitoring their glucose levels, or for collecting data on diabetes management on a community regional national or international basis.
- Trie modem assembly can be of any configuration (e.g.
- TCP/IP or ATM TCP/IP or ATM
- wireless communication capabilities e.g. those using GSM, WAP, CDMA, etc.
- GSM Global System for Mobile communications
- WAP Wireless Fidelity
- CDMA Code Division Multiple Access
- One such modem is described in copending commonly- assigned US Patent Application No. 09/512,9 9, filed February 25, 2000, the contents of which are hereby incorporated by reference.
- Other embodiments of the invention will be apparent to those skilled in the art from consideration of the specification and practice of the invention disclosed herein. It is intended that the specification and examples be considered as illustrative only, with a true scope and spirit of the invention being indicated by the following claims.
Abstract
Description
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Priority Applications (1)
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EP02709363A EP1364042A4 (en) | 2001-02-28 | 2002-02-28 | Method for determining concentration of an analyte in a test strip |
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Application Number | Priority Date | Filing Date | Title |
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US09/794,045 US6541266B2 (en) | 2001-02-28 | 2001-02-28 | Method for determining concentration of an analyte in a test strip |
US09/794,045 | 2001-02-28 |
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Cited By (16)
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EP1452854A1 (en) * | 2001-11-20 | 2004-09-01 | Arkray, Inc. | Fail judging method for analysis and analyzer |
WO2008017819A1 (en) * | 2006-08-08 | 2008-02-14 | Ivmd (Uk) Limited | Assay apparatus, assay reading apparatus and method |
WO2009101242A1 (en) * | 2008-02-14 | 2009-08-20 | Orion Diagnostica Oy | Method for predicting a future property |
US7645373B2 (en) | 2003-06-20 | 2010-01-12 | Roche Diagnostic Operations, Inc. | System and method for coding information on a biosensor test strip |
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CN109922730B (en) * | 2016-10-25 | 2022-03-22 | 豪夫迈·罗氏有限公司 | Method for determining an analyte concentration in a body fluid and analyte concentration measuring device |
US11284817B2 (en) | 2016-10-25 | 2022-03-29 | Roche Diabetes Care, Inc. | Method for determination of an analyte concentration in a body fluid and analyte concentration measurement device |
JP7141392B2 (en) | 2016-10-25 | 2022-09-22 | エフ ホフマン-ラ ロッシュ アクチェン ゲゼルシャフト | Method and device for determining analyte concentration in body fluids |
Also Published As
Publication number | Publication date |
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EP1364042A4 (en) | 2005-03-30 |
US6541266B2 (en) | 2003-04-01 |
US20020146835A1 (en) | 2002-10-10 |
EP1364042A1 (en) | 2003-11-26 |
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