Classifications

• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
  • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
  • G01N27/28—Electrolytic cell components
  • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
  • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
  • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
  • G01N27/3274—Corrective measures, e.g. error detection, compensation for temperature or hematocrit, calibration
• • G—PHYSICS
  • G01—MEASURING; TESTING
  • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
  • G01N27/00—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means
  • G01N27/26—Investigating or analysing materials by the use of electric, electrochemical, or magnetic means by investigating electrochemical variables; by using electrolysis or electrophoresis
  • G01N27/28—Electrolytic cell components
  • G01N27/30—Electrodes, e.g. test electrodes; Half-cells
  • G01N27/327—Biochemical electrodes, e.g. electrical or mechanical details for in vitro measurements
  • G01N27/3271—Amperometric enzyme electrodes for analytes in body fluids, e.g. glucose in blood
  • G01N27/3273—Devices therefor, e.g. test element readers, circuitry
• • 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
  • Y10T436/11—Automated chemical analysis
• • 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
  • Y10T436/11—Automated chemical analysis
  • Y10T436/112499—Automated chemical analysis with sample on test slide
• • 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.]
• • 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.]
• • 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 to a measurement method and apparatus for use in measuring concentrations of an analyte in a fluid.
• the invention relates 20 more particularly, but not exclusively, to a method and apparatus which may be used for measuring the concentration of glucose in blood.
• Measuring the concentration of substances, particularly in the presence of other, confounding substances, is important in many fields, and especially in medical diagnosis.
• the measurement of glucose in body fluids, such as blood is crucial to the effective treatment of diabetes.
• Diabetic therapy typically involves two types of insulin treatment: basal, 30 and meal-time.
• Basal insulin refers to continuous, e.g. time-released insulin, often taken before bed.
• Meal-time insulin treatment provides additional doses of faster acting insulin to regulate fluctuations in blood glucose caused by a variety of factors, including the metabolization of sugars and carbohydrates. Proper regulation of blood glucose fluctuations requires accurate measurement of the concentration of glucose in the blood.
• Optical methods generally involve reflectance or absorbance spectroscopy to observe the spectrum shift in a reagent. Such shifts are caused by a chemical reaction that produces a color change indicative of the concentration of the analyte.
• Electrochemical methods generally involve, alternatively, amperometric or coulometric responses indicative of the concentration of the analyte. See, for example, U.S. Patent Nos.
• An important limitation of electrochemical methods of measuring the concentration of a chemical in blood is the effect of confounding variables on the diffusion of analyte and the various active ingredients of the reagent.
• the geometry and state of the blood sample must correspond closely to that upon which the signal-to-concentration mapping function is based.
• the geometry of the blood sample is typically controlled by a sample- receiving portion of the testing apparatus.
• the blood sample is typically placed onto a disposable test strip that plugs into the meter.
• the test strip may have a sample chamber (capillary fill space) to define the geometry of the sample.
• the effects of sample geometry may be limited by assuring an effectively infinite sample size.
• the electrodes used for measuring the analyte may be spaced closely enough so that a drop of blood on the test strip extends substantially beyond the electrodes in all directions. Ensuring adequate coverage of the measurement electrodes by the sample, however, is an important factor in achieving accurate test results. This has proven to be problematic in the past, particularly with the use of capillary fill spaces.
• Other examples of limitations to the accuracy of blood glucose measurements include variations in blood composition or state (other than the aspect being measured). For example, variations in hematocrit (concentration of red blood cells), or in the concentration of other chemicals in the blood, can effect the signal generation of a blood sample. Variations in the temperature of blood samples is yet another example of a confounding variable in measuring blood chemistry.
• a system and method are needed that accurately measure blood glucose, even in the presence of confounding variables, including variations in temperature, hematocrit, and the concentrations of other chemicals in the blood.
• a system and method are also needed to ensure adequate coverage of the measurement electrodes by the sample, particularly in capillary fill devices.
• a system and method are likewise needed that accurately measure an analyte in a fluid. It is an object of the present invention to provide such a system and method.
• a method for determining a glucose concentration of a blood sample comprising the steps of a) applying a signal having an AC component to the blood sample; b) measuring an AC phase angle response to the signal; and c) determining the glucose concentration using the AC phase angle response.
• a method of determining a glucose concentration of a biological fluid sample comprising (a) applying a signal having an AC component to the sample; (b) measuring an AC phase angle response to the signal; and determining the glucose concentration based upon the AC phase angle response and a predetermined correlation between the AC phase angle response and the glucose concentration.
• a method of determining a glucose concentration of a test sample comprising (a) applying a signal having an AC component to the sample; (b) measuring an AC phase angle response to the signal; and (c) determining the glucose concentration using the first AC phase angle response and a predetermined compensation factor.
• a method for determining a hematocrit value of a blood sample comprising the steps of a) applying at least one signal having an AC component to the blood sample; b) measuring at least one AC phase angle response to respective ones of the at least one signal; and c) determining the hematocrit value using the at least one AC phase angle response.
• a method for determining a hematocrit value of a blood sample comprising the steps of (a) applying a first signal having an AC component to the blood sample, the first signal having a first frequency; (b) measuring a first AC phase angle response to the first signal; (c) applying a second signal having an AC component to the blood sample, the second signal having a second frequency; (d) measuring a second AC phase angle response to the second signal; and (e) determining the hematocrit value based at least in part upon the first phase angle response and the second phase angle response.
• Fig. 1 is a diagram of a first embodiment excitation signal suitable for use in a system and method according to the present invention, having a serially-applied AC component and DC component.
• Fig. 2 is a diagram of a second embodiment excitation signal suitable for use in a system and method according to the present invention, having a simultaneously-applied AC component and DC component.
• Figs. 3 A-B illustrate a first embodiment test strip of the present invention.
• Fig. 4 is a diagram of an excitation signal utilized in the test of Example 1.
• Fig. 5 is a plot of the correlation coefficient r 2 (glucose vs. DC current) versus Read Time for the test of Example 1 with no incubation time.
• Fig. 6 is a plot of the correlation coefficient r (glucose vs. DC current) versus Read Time for the test of Example 1 with varying incubation time.
• Fig. 7 is a plot of AC admittance versus hematocrit for the test of Example 2.
• Fig. 8 is a plot of uncompensated DC current versus glucose for the test of Example 2.
• Fig. 9 is a plot of the predicted glucose response versus the actual glucose response for the test of Example 2.
• Fig. 10 is a diagram of an excitation signal utilized in the test of Example 3.
• Fig. 11 is a plot of the AC phase angle versus reference glucose for the test of Example 3.
• Fig. 12 is a plot of the predicted glucose response versus the actual glucose response for the test of Example 3.
• Fig. 13 is a diagram of an excitation signal utilized in the test of Example 4.
• Fig. 14 is a plot of AC admittance versus hematocrit (parametrically displayed with temperature) for the test of Example 4.
• Fig. 15 is a plot of the uncompensated DC response versus actual glucose for the test of Example 4.
• Fig. 16 is a plot of the predicted glucose response versus actual glucose response for the test of Example 4.
• Figs. 17A-B illustrate a second embodiment test strip of the present invention.
• Fig. 18 is a plot parametrically illustrating the correlation coefficient r 2 between the DC current response and glucose level as Read Time varies for three combinations of temperature and hematocrit in the test of Example 5.
• Fig. 19 is a diagram of the excitation signal utilized in the test of Example 5.
• Fig. 20 is a plot of AC admittance versus hematocrit as temperature is parametrically varied in the test of Example 5.
• Fig. 21 is a plot of AC admittance phase angle versus hematocrit as temperature is parametrically varied in the test of Example 5.
• Fig. 22 is a plot of the uncompensated DC response versus actual glucose for the test of Example 5.
• Fig. 23 is a plot of the predicted glucose response versus actual glucose response for the test of Example 5.
• Fig. 24 is a diagram of the excitation signal utilized in the test of Example 6.
• Fig. 25 is a plot of the correlation coefficient r 2 between hematocrit and DC response current plotted against hematocrit in the test of Example 6.
• Fig. 26 is a plot of AC admittance phase angle versus hematocrit for the test of Example 6.
• Fig. 27 is a plot of the uncompensated DC response versus actual glucose for the test of Example 6.
• Fig. 28 is a plot of the compensated DC response versus actual glucose for a 1J second Total Test Time of Example 6.
• Fig. 29 is a plot of the compensated DC response versus actual glucose for a 1.5 second Total Test Time of Example 6.
• Fig. 30 is a plot of the compensated DC response versus actual glucose for a 1.9 second Total Test Time of Example 6.
• Fig. 31 is a table detailing the heights and widths of the capillary fill channels used in the test devices of Example 8, as well as schematic diagrams of convex and concave sample flow fronts in a capillary fill space.
• Figs. 32A-C are schematic plan views of a test strip illustrating the potential for biased measurement results when a concave flow front encounters a prior art dose sufficiency electrode.
• Fig. 33 is a schematic plan view of a test strip of the present invention having a pair of perpendicular dose sufficiency electrodes that are independent from the measurement electrodes.
• Figs. 34A-B are schematic plan views of the test strip of FIG. 33 containing samples with convex and concave flow fronts, respectively.
• Figs. 35 A-B are schematic plan views of a test strip of the present invention having a pair of parallel dose sufficiency electrodes that are independent from the measurement electrodes.
• Fig. 36 is a schematic plan view of the test strip of Fig. 35, schematically illustrating the electric field lines that communicate between the electrode gap when the electrodes are covered with sample.
• a system and method according to the present invention permit the accurate measurement of an analyte in a fluid.
• the measurement of the analyte remains accurate despite the presence of interferants, which would otherwise cause error.
• a blood glucose meter measures the concentration of blood glucose without error that is typically caused by variations in the temperature and the hematocrit level of the sample.
• the accurate measurement of blood glucose is invaluable to the prevention of blindness, loss of circulation, and other complications of inadequate regulation of blood glucose in diabetics.
• An additional advantage of a system and method according to the present invention is that measurements can be made much more rapidly and with much smaller sample volumes, making it more convenient for the diabetic person to measure their blood glucose.
• accurate and rapid measurement of other analytes in blood, urine, or other biological fluids provides for improved diagnosis and treatment of a wide range of medical conditions.
• electrochemical blood glucose meters typically (but not always) measure the electrochemical response of a blood sample in the presence of a reagent.
• the reagent reacts with the glucose to produce charge carriers that are not otherwise present in blood. Consequently, the electrochemical response of the blood in the presence of a given signal is intended to be primarily dependent upon the concentration of blood glucose.
• the electrochemical response of the blood to a given signal is dependent upon other factors, including hematocrit and temperature. See, for example, U.S. Patents Nos.
• a preferred embodiment system and method for measuring blood glucose according to the present invention operates generally by using the signal- dependence of the contribution of various factors to the impedance (from which admittance and phase angle may be derived) of a blood sample.
• the effects of confounding factors can be substantially reduced by measuring the impedance of the blood sample to multiple signals.
• the effects of confounding factors (primarily temperature and hematocrit, but also including chemical interferants such as oxygen), contribute primarily to the resistivity of the sample, while the glucose-dependent reaction contributes primarily to the capacitance.
• the effects of the confounding factors can be eliminated by measuring the impedance of the blood sample to an AC excitation, either alone or in combination with a DC excitation.
• the impedance (or the impedance derived admittance and phase information) of the AC signal is then used to correct the DC signal or AC derived capacitance for the effects of interferants. It will be appreciated that measurements at sufficiently high AC frequencies are relatively insensitive to the capacitive component of the sample's impedance, while low frequency (including DC) measurements are increasingly (with decreasing frequency) sensitive to both the resistive and the capacitive components of the sample's impedance.
• the resistive and capacitive components of the impedance can be better isolated by measuring the impedance at a larger number of frequencies. However, the cost and complexity of the meter increases as the number of measurements increases and the number of frequencies that need to be generated increases.
• the impedance may be measured at greater than ten frequencies, but preferably at between two and ten frequencies, and most preferably at between two and five frequencies.
• a signal having an AC component refers to a signal which has some alternating potential (voltage) portions.
• the signal may be an "AC signal” having 100% alternating potential (voltage) and no DC portions; the signal may have AC and DC portions separated in time; or the signal may be AC with a DC offset (AC and DC signals superimposed).
• Figure 1 illustrates a preferred embodiment excitation signal suitable for use in a system and method according to the present invention, indicated generally at 100, in which DC excitation and four frequencies of AC excitation are used.
• Figure 1 also illustrates a typical response to the excitation when the excitation is applied to a sample of whole blood mixed with an appropriate reagent, the response indicated generally at 102.
• a relatively high frequency signal is applied, starting at time 101.
• the frequency is between about 10kHz and about 20kHz, and has an amplitude between about 12.4mV and about 56.6mV.
• a frequency of 20kHz is used in the example of FIG. 1.
• Those skilled in the art will appreciate that these values may be optimised to various parameters such as cell geometry and the particular cell chemistry.
• a test strip is inserted into the meter and several possible responses to the insertion of the test strip into the glucose meter are shown.
• the test strip may also be inserted before the excitation signal 100 is initiated (i.e. before time 101); however, the test strip itself may advantageously be tested as a control for the suitability of the strip. It is therefore desirable that the excitation signal 100 be initiated prior to test strip insertion.
• relatively large current leakage as shown at 112 may occur if the strip is wet, either because the test strip was pre-dosed, or due to environmental moisture. If the test strip has been pre-dosed and permitted to largely or completely dry out, an intermediate current leakage may occur, as shown at 114.
• insertion of the test strip will cause no or negligible leakage current due to an expected absence of charge carriers between the test electrodes, as shown at 116. Measured current leakage above a predetermined threshold level will preferably cause an error message to be displayed and prevent the test from continuing.
• the user doses the strip, as shown at time 120. While the blood sample is covering the electrodes the current response will rapidly increase, as the glucose reacts with the reagent and the contact area increases to maximum. The response current will reach a stable state, which indicates the impedance of the sample at this frequency. Once this measurement is made and recorded by the test meter, the excitation frequency is then stepped down to about 10kHz in the preferred embodiment, as shown at time 130.
• Another measurement is made and recorded by the test meter, and the frequency is stepped down to about 2kHz in the preferred embodiment, as shown at 140.
• a third measurement is made and recorded by the test meter at this frequency.
• a fourth measurement is made at about 1kHz in the preferred embodiment, as shown at 150.
• measurements are taken at regular intervals (e.g. 10 points per cycle). It will be appreciated that the stable state response may be measured as current or voltage (preferably both magnitude and phase) and the impedance and/or admittance can be calculated therefrom.
• the test meter applies a voltage to one electrode and measures the current response at the other electrode to obtain both the AC and DC response.
• measurements are made at fewer or more frequencies.
• measurements are made at at least two AC frequencies at least an order of magnitude apart. If more than two AC frequencies are used, then it is preferable that the highest and lowest frequencies be at least an order of magnitude apart.
• various waveforms may be used in an AC signal, including, for example, sinusoidal, trapezoidal, triangle, square and filtered square.
• the AC signal has a filtered square waveform that approximates a sine wave. This waveform can be generated more economically than a true sine wave, using a square wave generator and one or more filters.
• the signal is preferably briefly reduced to zero amplitude, as shown at 160.
• the DC excitation is then begun, as shown at 170.
• the amplitude of the DC excitation is advantageously selected based on the reagent being used, in order to maximise the resulting response or response robustness.
• the DC amplitude is preferably about 300mV.
• the DC amplitude is preferably about 500-550mV.
• the DC applitude is preferably 600 mN (versus the silver/silver chloride reference electrode) for ferricyanide, and 40-100 mV (versus the silver/silver chloride reference electrode) for nitrosoaniline derivative.
• measurements are preferably made at a rate of 100 pts/sec.
• the current response will follow a decay curve (known as a Cottrell curve), as the reaction is limited by the diffusion of unreacted glucose next to the working electrode.
• the resulting stable-state amplitude (measured or projected) is used to determine a glucose estimation of the sample, as is known in the art.
• a corrected estimation is then determined that corresponds more closely to the concentration of glucose in the blood, by using the impedance of the sample to the AC signal to correct for the effects of interferants, as explained in greater detail hereinbelow. It will be appreciated that a method according to the present invention may also be used to measure the concentration of other analytes and in other fluids.
• a method according to the present invention may be used to measure the concentration of a medically significant analyte in urine, saliva, spinal fluid, etc.
• a method according to the present invention may be adapted to measure the concentration of, for example, lactic acid, hydroxybutyric acid, etc.
• Figure 2 illustrates an excitation signal suitable for use in a system and method according to the present invention in which some of the AC and DC components are applied simultaneously, indicated generally at 200, and having corresponding events numbered correspondingly to Figure 1 (so, for example, the signal 200 is initiated at time 201, and a strip is inserted at time 210, etc.).
• the signal 200 has a frequency of about 10-20kHz and an amplitude of about 12.4-56.6mV.
• a DC offset is superimposed, as shown at 270.
• Typical AC and DC responses are shown in Figure 2.
• a system for measuring blood glucose advantageously employs a blood glucose meter and test strips generally similar to those used in prior art systems, such as those commercially available from Roche Diagnostics, and such as are described in U.S. Patents Nos. 6,270,637; and 5,989,917, which are hereby incorporated in their entireties.
• test strips provide apparati having a sample cell in which the blood sample is received for testing, and electrodes disposed within the sample cell through which the excitation signal is provided and the measurements are made.
• test strips and meters may advantageously be used for the measurement of glucose in blood, but that other apparati may be more suitable for the measurement of other analytes or other biological fluids when practising the present invention.
• a suitable glucose meter may be adapted from such known meters by the addition of electronic circuitry that generates and measures signals having AC and DC components, such as those described hereinabove, and by being programmed to correct the DC measurement using the AC measurement(s), as described in greater detail hereinbelow. It will be appreciated that the specific geometry and chemistry of the test strips can cause variations in the relationships between the concentration of glucose, hematocrit, and temperature, and the impedance of a sample.
• the present invention comprehends the application of excitation signals in any order and combination.
• the present invention comprehends the application of 1) AC only, 2) AC then DC, 3) AC then DC then AC, 4) DC then AC, and 5) AC with a DC offset, just to name a few of the possible permutations.
• the use of the complex AC impedance measurement data to correct for the effects of interferants on the DC measurement is advantageously illustrated by the following series of examples. These examples illustrate how the principles of the present invention can facilitate improvements in accuracy and test speed when measuring the concentration of an analyte in a test specimen.
• the process may never actually arrive at a number equal to the hematocrit value of the sample, but instead determine that the sample's hematocrit differs from a nominal value by a certain amount. Both concepts are intended to be covered by statements such as "determine the hematocrit value.”
• Example 1 The measurements made in Example 1 were achieved using the test strip illustrated in Figures 3A-B and indicated generally at 300.
• the test strip 300 includes a capillary fill space containing a relatively thick film reagent and working and counter electrodes, as described in U.S. Patent No. 5,997,817, which is hereby incorporated by reference.
• the test strip 300 is commercially available from Roche Diagnostics Corporation (Indianapolis, IN) under the brand name Comfort Curve ®.
• the ferricyanide reagent used had the composition described in Tables I and E.
• the first parameter was the Incubation Time, or the time between the detection of the blood sample being applied to the test strip 300 and the application of the DC potential to the test strip 300.
• the second parameter to be varied was the Read Time, or the time period after application of the DC potential and the measurement of the resulting current.
• the length of time between detection of the blood sample being applied to the test strip to the taking of the last measurement used in the concentration determination calculations is the Total Test Time. In this study, therefore, the sum of the Incubation Time and the Read Time is the Total Test Time.
• Figures 5 The results of this study are illustrated in Figures 5 and 6.
• Figure 5 plots the correlation coefficient r 2 versus Read Time.
• the correlation exceeds 0.95 within 1.0 second.
• the DC response was measured with varying Incubation Time.
• an Incubation Time is provided (even an Incubation Time as short as two (2) seconds), the r 2 value rose to over 0.99 in 0.5 seconds or less after application of the DC potential.
• the barrier to implementation of such fast test times in a consumer glucose test device is the variation from blood sample to blood sample of the level of interference from the presence of blood cells in the sample.
• the hematocrit (the percentage of the volume of a blood sample which is comprised of cells versus plasma) varies from individual to individual.
• the interference effect of hematocrit on such measurements is fairly complex. In the tests of Example 1, however, all samples contained the same level of hematocrit. With no variable hematocrit influence at the different glucose levels, the hematocrit term cancels out in the correlation figures.
• test strip 300 includes a capillary fill space containing a relatively thick film reagent and working and counter electrodes, as described in U.S. Patent No. 5,997,817, which is hereby incorporated herein by reference.
• capillary blood samples from various fingerstick donors were applied to test strip 300 and the excitation potentials illustrated in Figure 4 were applied to the electrodes.
• the excitation comprised a 2 kHz 40 mV ⁇ ns AC signal applied between 0 seconds and approximately 4.5 seconds after sample application, followed by a 300 mV DC signal applied thereafter.
• the AC response of the sample was derived as admittance (the inverse of impedance).
• the admittance response is proportionate to the hematocrit level of the sample in a temperature dependent manner.
• the relationship between admittance, hematocrit and testing temperature is illustrated in Figure 7.
• the data used for the admittance charted in Figure 7 is the last admittance measurement made for each sample during the AC portion of the excitation illustrated in Figure 4. Regression analysis of this data allows admittance, hematocrit and temperature to be related according to the following formula:
• Equation 1 Using this relationship to predict the blood hematocrit is accomplished using test temperature data reported by the temperature sensor in the meter and the measured admittance.
• c 0 , c ⁇ and c 2 are constants
• dl is the deviation in temperature from a center defined as “nominal” (24°C for example)
• H eS - is the estimated deviation in hematocrit from a similar "nominal” value.
• the actual hematocrit value is not necessary, and it is generally preferred to produce a response which is proportionate but centers around a nominal hematocrit.
• Equation 2 where DC is the measured glucose current response to the applied DC signal and PRED is the compensated (predicted) glucose response corrected for the effects of hematocrit and temperature.
• the constants (ao, hct 1; hct 2> tau 1; tau 2 , a ⁇ hct 3 , hct 4 , tau 3 and tau 4 ) in Equation 2 can be determined using regression analysis, as is known in the art.
• Figure 8 illustrates the uncompensated 5.5 second DC glucose response of all of the capillary blood samples as temperature varies (ignoring the AC measurement data). As will be appreciated, there is a wide variation in the DC current response as temperature and hematocrit vary.
• Figure 9 illustrates the correlation between the actual blood glucose level of the sample versus the predicted response using Equation 2. As can be seen, when the DC response is compensated for hematocrit levels using the AC response data, r 2 values of 0.9404 to 0.9605 are achieved with a Total Test Time of 5.5 seconds.
• Example 3 Use of AC Phase Angle (o Estimate Blood Glucose Levels and Hematocrit
• Example 3 The measurements made in Example 3 were also achieved using the test strip illustrated in Figures 3A-B and indicated generally at 300.
• the test strip 300 includes a capillary fill space containing a relatively thick film reagent and working and counter electrodes, as described in U.S. Patent No. 5,997,817, which is hereby incorporated by reference. Because hematocrit levels from capillary blood samples typically vary only between 30% - 50%, spiked venous blood samples having a hematocrit range from 20% - 70% were used for this Example 3. Five levels of glucose, temperature (14, 21, 27, 36 and 42 °C) and hematocrit (20, 30, 45, 60 and 70%) were independently varied, producing a covariance study with 125 samples.
• the excitation comprised a 2 kHz AC signal for approximately 4J seconds, a 1 kHz AC signal for approximately 0J seconds, and a 200 Hz signal for approximately 0J seconds. All three AC signals had an amplitude of 56.56 mV peak. No DC excitation was used in this example.
• the Total Test Time was 4.3 seconds from sample application time. It was found that another component of the AC response, the phase angle (particularly at lower frequencies, such as 200 Hz in this Example 3), is also a function of the sample glucose level in the case of this test strip and reagent.
• the present invention therefore comprehends the use of the AC phase angle to measure glucose levels.
• the AC excitation frequency producing the measured phase angle is preferably 2 kHz or below, more preferably 1 kHz or below, and most preferably 200 Hz or below, but not including DC excitation.
• R e/ is the effective phase, which is proportional to glucose
• T and ⁇ are constants
• ⁇ is the measured AC phase angle
• the resulting compensated (predicted) response PRED versus glucose for the 125 blood samples is shown in Figure 12.
• This Example 3 demonstrates again the value of AC measurements for compensating for interferants that reduce the accuracy of blood glucose measurements. Using an existing commercially available sensor, the present invention yields a 4.3 second Total Test Time with an overall r 2 of 0.9870. It was also determined that AC phase angle measurements can produce hematocrit level measurements that are almost immune to the effects of temperature variation.
• each of the samples was tested using an excitation profile of 20 kHz, 10kHz, 2 kHz, 1kHz and DC.
• the AC phase angle at various frequencies was related to glucose, hematocrit and temperature using linear regression to determine the coefficients of the following formula at each of the four AC frequencies:
• Glu is the known glucose concentration
• HCT is the known hematocrit concentration
• Temp is the known temperature.
• the determined coefficients revealed that the temperature coefficient (c 3 ) was essentially zero at 20 kHz and 10 kHz, cancelling temperature from the equation at these frequencies.
• the glucose coefficient (c ) is essentially zero at all of the AC frequencies because, as explained hereinabove, the higher frequency AC impedance measurements are largely unaffected by glucose levels and are therefore useful for measuring the levels of interfering substances. It was therefore found that the hematocrit level could be determined independent of temperature and glucose level using only the AC phase angle measurements. In a preferred embodiment, the hematocrit may be measured using the phase angle data from all four measured frequencies:
• E-est c 0 + C1 ⁇ 20MHZ + c 2 ⁇ i ⁇ kHz + c 3 ⁇ 2 kHz + c 4 ⁇ lkHz (Equation 6)
• the coefficients can be empirically determined for any particular test strip architecture and reagent chemistry.
• the present invention therefore may be used to estimate hematocrit using only AC phase angle measurements preferably made at at least one AC frequency, more preferably made at at least two AC frequencies, and most preferably made at at least four AC frequencies.
• Example 4 Combined AC and DC Measuremeni Using Niirosoaniline Reagen( The measurements made in Example 4 were also achieved using the test strip illustrated in Figures 3A-B and indicated generally at 300.
• the test strip 300 includes a capillary fill space containing a relatively thick film reagent and working and counter electrodes, as described in U.S. Patent No. 5,997,817, which is hereby incorporated by reference.
• the test strip was modified from that described in U.S. Patent No. 5,997,817, however, by the use of a different reagent.
• the nitrosoaniline reagent used had the composition described in Tables LU and IV.
• Step 1 Prepare a buffer solution by adding 1.54g of dibasic potassium phosphate (anhydrous) to 43.5 g of deionized water. Mix until the potassium phosphate is dissolved.
• Step 2 To the solution from step 1, add lJ4g of monobasic potassium phosphate and mix until dissolved.
• Step 3 To the solution from step 2, add 0.59g of disodium succinate (hexahydrate) and mix until dissolved.
• Step 4 Verify that the pH of the solution from step 3 is 6.7 +/- 0J. Adjustment should not be necessary.
• Step 5 Prepare a 5g aliquot of the solution from step 4, and to this add 113 kilounits (by DCIP assay) of the apoenzyme of quinopro(ein glucose dehydrogenase (EC#: 1J.99.17). This is approximately 0J646g. Mix, slowly, until the protein is dissolved.
• Step 6 To the solution from step 5, add 4.2 milligrams of PQQ and mix for no less than 2 hours to allow the PQQ and the apoenzyme to reassociate in order to provide functional enzyme.
• Step 7 To the solution from step 4, add 0.66g of the mediator precursor, N,N- bis(hydroxyethyl)-3-methoxy-4-nitrosoaniline (hydrochloride) (BM 31.1144). Mix until dissolved (this solution will have a greenish black coloration).
• Step 8 Measure the pH of the solution from step 7 and adjust the pH to a target of 7.0 +/- 0J. Normally this is accomplished with 1.197g of 5N potassium hydroxide. Because the specific amount of potassium hydroxide may vary as needed to reach the desired pH, generally deviations in mass from the lJ97g are made up from an aliquot of 3.309g deionized water which is also added at this step.
• Step 9 Prepare a solution of Natrosol 250M (available from Aqualon), by slowly sprinkling 0.047g over 44.57g of deionized water which is mixed (using a rotary mixer and blade impeller) at a rate of approximately 600 rpm in a vessel of sufficient depth such that the rotor blades are not exposed nor the solution running over. Mix until the Natrosol is completely dissolved.
• Step 10 Prepare a suspension of Avicel RC-591F (available from FMS), by slowly sprinkling 0.54g onto the surface of the solution from step 9, mixing at a rate of approximately 600 rpm for not less than 60 minutes before proceeding.
• Step 11 To the suspension from step 10, gradually add 0.81g of Polyethylene oxide of 300kDa mean molecular weight while mixing and continue to mix for not less than 60 minutes before proceeding.
• Step 12 Gradually add the solution from step 8 to the suspension from step 11 while mixing. Reduce the mixing rate to 400 rpm.
• Step 13 To the reagent from step 12, add 1.89g of Trehalose and continue mixing for not less than 15 minutes.
• Step 14 To the reagent from step 13, add 32.7mg of Triton X-100 (available from Roche Diagnostics) and continue mixing.
• Triton X-100 available from Roche Diagnostics
• Step 15 To the reagent from step 14, add the enzyme solution from step 6. Mix for no less than 30 minutes. At this point the reagent is complete. At room teperature the wet reagent mass is considered acceptable for use for 24 hours.
• Spiked venous blood samples were used. Five levels of glucose, four temperatures (19, 23, 32 and 38 °C) and five levels of hematocrit (20, 30, 45, 60 and 70%) were independently varied, producing a covariance study with 100 samples. 16 test strips 300 were tested for each unique combination of glucose, temperature and hematocrit. The blood samples were applied to test strip 300 and the excitation potentials illustrated in Figure 13 were applied to the electrodes.
• the excitation comprised a 3.2 kHz AC signal for approximately 4.0 seconds, a 2J3 kHz AC signal for approximately 0J seconds, a 1.07 kHz AC signal for approximately 0J seconds, a 200 Hz AC signal for approximately 0J seconds, a 25 Hz AC signal for approximately 0J seconds, followed by a DC signal of 550 mV for approximately 1.0 second. All four AC signals had an amplitude of 56.56 mV peak.
• the Total Test Time was 5.5 seconds from sample application time.
• the AC response of the sample was derived as admittance (the inverse of impedance). The admittance response is proportionate to the hematocrit level of the sample in a temperature dependent manner.
• Equation 7 c 0 , ci, c 2 and c 3 are constants, d ⁇ is the deviation in temperature from a center defined as “nominal” (24°C for example), and H est is the estimated deviation in hematocrit from a similar "nominal" value.
• the actual hematocrit value is not necessary, and it is generally preferred to produce a response which is proportionate but centers around a nominal hematocrit.
• Equation 8 can be determined using regression analysis, as is known in the art.
• Figure 15 illustrates the uncompensated 5.5 second DC glucose response of all of the blood samples as hematocrit and temperature vary (ignoring the AC measurement data). As will be appreciated, there is a wide variation in the DC current response as temperature and hematocrit vary.
• Figure 16 illustrates the correlation between the actual blood glucose level of the sample versus the predicted response using Equation 8. As can be seen, when the DC response is compensated for hematocrit levels using the AC response data, an overall r 2 value of 0.9818 is achieved with a Total Test Time of 5.5 seconds. This demonstrates the applicability of the present invention in achieving high accuracy and fast test times with a different reagent class than was used in Examples 1-3.
• Example 5 Combined AC and DC Measurement Using a 0.397 ⁇ l Sample
• test strip 1700 comprises a bottom foil layer 1702 formed from an opaque piece of 350 ⁇ m thick polyester (in the preferred embodiment this is Melinex 329 available from DuPont) coated with a 50 nm conductive (gold) layer (by sputtering or vapor deposition, for example). Electrodes and connecting traces are then patterned in the conductive layer by a laser ablation process to form working, counter, and dose sufficiency electrodes (described in greater detail hereinbelow) as shown.
• Melinex 329 available from DuPont
• the laser ablation process is performed by means of an excimer laser which passes through a chrome-on-quartz mask.
• the mask pattern causes parts of the laser field to be reflected while allowing other parts of the field to pass through, creating a pattern on the gold which is ejected from the surface where contacted by the laser light.
• Examples of the use of laser ablation techniques in preparing electrodes for biosensors are described in United States Patent Application Serial Number 09/866,030, "Biosensors with Laser Ablation Electrodes with a Continuous Coverlay Channel” filed May 25, 2001, and in United States Patent Application Serial Number 09/411,940, entitled “Laser Defined Features for Patterned Laminates and Electrode,” filed October 4, 1999, both disclosures incorporated herein by reference.
• the bottom foil layer 1702 is then coated in the area extending over the electrodes with a reagent layer 1704 in the form of an extremely thin reagent film.
• This procedure places a stripe of approximately 7.2 millimeters width across the bottom foil 1702 in the region labelled "Reagent Layer" on Figure 17. In the present Example, this region is coated at a wet-coat weight of 50 grams per square meter of coated surface area leaving a dried reagent less than 20 ⁇ m thick.
• the reagent stripe is dried conventionally with an in-line drying system where the nominal air temperature is at 110°C. The rate of processing is nominally 30-38 meters per minute and depends upon the rheology of the reagent.
• the materials are processed in continuous reels such that the electrode pattern is orthogonal to the length of the reel, in the case of the bottom foil 1702.
• the spacer is slit and placed in a reel-to-reel process onto the bottom foil 1702.
• Two spacers 1706 formed from 100 ⁇ m polyester (in the preferred embodiment this is Melinex 329 available from DuPont) coated with 25 ⁇ m PSA (hydrophobic adhesive) on both the dorsal and ventral surfaces are applied to the bottom foil layer 1702, such that the spacers 1706 are separated by 1.5 mm and the working, counter and dose sufficiency electrodes are centered in this gap.
• the hydrophilic film is coated with a mixture of Vitel and Rhodapex surfactant at a nominal thickness of 10 microns.
• the top foil layer 1708 is laminated using a reel-to-reel process. The sensors can then be produced from the resulting reels of material by means of slitting and cutting.
• the 1.5 mm gap in the spacers 1706 therefore forms a capillary fill space between the bottom foil layer 1702 and the top foil layer 1708.
• the hydrophobic adhesive on the spacers 1706 prevents the test sample from flowing into the reagent under the spacers 1706, thereby defining the test chamber volume. Because the test strip 1700 is 5 mm wide and the combined height of the spacer 1706 and conductive layer is 0J5 mm, the sample receiving chamber volume is
• the distance from the sample application port 1710 and the dose sufficiency electrodes is 1.765 mm.
• the volume of sample needed to sufficiently cover the working, counter and dose sufficiency electrodes i.e. the minimum sample volume necessary for a measurement.
• the reagent composition for the test strip 1700 is given in Tables V and VI.
• nitrosoaniline reagent is as follows:
• Step 1 Prepare a buffer solution by adding 1.654g of dibasic potassium phosphate (trihydrous) to 31.394 g of deionized water. Mix until the potassium phosphate is dissolved.
• Step 2 To the solution from step 1, add 0.941g of monobasic potassium phosphate and mix until dissolved.
• Step 3 To the solution from step 2, add 0.285g of disodium succinate (hexahydrate) and mix until dissolved.
• Step 4 Verify that the pH of the solution from step 3 is 6.8 +/- 0J. Adjustment should not be necessary.
• Step 5 Prepare a 4.68g aliquot of the solution from step 4, and to this add 229 kilounits (by DCIP assay) of the apoenzyme of quinopro(ein glucose dehydrogenase (EC#: 1J.99.17). This is approximately 0.3321g. Mix, slowly, until the protein is dissolved.
• Step 6 To the solution from step 5, add 9.3 milligrams of PQQ and mix for no less than 2 hours to allow the PQQ and the apoenzyme to reassociate in order to provide functional enzyme.
• Step 7 Prepare a solution by dissolving 0.772g of Trehalose into 1.218g of deionized water.
• Step 8 After enzyme reassociation, add the solution from step 7 to the solution from step 6 and continue mixing for not less than 30 minutes.
• Step 9 To the solution from step 4, add 0.690g of the mediator precursor BM 31.1144. Mix until dissolved (this solution will have a greenish black coloration).
• Step 10 Measure the pH of the solution from step 9 and adjust the pH to a target of 7.0 +/- 0J. Normally this is accomplished with 1.006g of 5N potassium hydroxide. Because the specific amount of potassium hydroxide may vary as needed to reach the desired pH, generally deviations in mass from the 1.006g are made up from an aliquot of 3.161 g deionized water which is also added at this step.
• Step 11 Prepare a solution of Natrosol 250M (available from Aqualon), by slowly sprinkling 0.350g over 56J91g of deionized water which is mixed (using a rotary mixer and blade impeller) at an initial rate of approximately 600 rpm in a vessel of sufficient depth such that the rotor blades are not exposed nor the solution running over. As the Natrosol dissolves, the mixing rate needs to be increased to a speed of 1.2 - 1.4 krpm. Mix until the Natrosol is completely dissolved. Note that the resulting matrix will be extremely viscous - this is expected.
• Natrosol 250M available from Aqualon
• Step 12 To the solution from step 11, gradually add 0.350g of Sodium- Carboxymethylcellulose 7HF (available from Aqualon). Mix until the polymer is dissolved.
• Sodium- Carboxymethylcellulose 7HF available from Aqualon
• Step 13 To the suspension from step 13, gradually add 1.0 lg of Polyethylene oxide of 300kDa mean molecular weight while mixing and continue to mix for not less than 60 minutes before proceeding.
• Step 14 Gradually add the solution from step 10 to the suspension from step 13 while mixing.
• Step 15 To the reagent from step 14, add 34.2mg of Triton X-100 (available from Roche Diagnostics) and continue mixing.
• Step 16 To the reagent from step 15, add the enzyme solution from step 8. Mix for no less than 30 minutes. At this point the reagent is complete. At room teperature the wet reagent mass is considered acceptable for use for 24 hours.
• the measurement results illustrated in FIG. 18 show the correlation coefficient r 2 between the DC current response and the glucose level as the Read Time varies for three combinations of temperature and hematocrit.
• the AC signals had an amplitude of 12.7 mV peak, while the DC signal had an amplitude of 550 mV.
• the Total Test Time was 3.0 seconds.
• the relationship between admittance, temperature and hematocrit was examined and plotted (Figure 20 shows the admittance at 20 kHz versus hematocrit as temperature varies) and it was confirmed that the admittance was linearly related to hematocrit in a temperature dependent manner.
• phase angle of the AC response was correlated with hematocrit in a temperature independent manner.
• the phase angle of the 20 kHz AC response is plotted versus hematocrit in Figure 21.
• the results for phase angle measured at 10 kHz are similar.
• the hematocrit of the blood sample may therefore be reliably estimated using only the phase angle information as follows:
• the correlation between phase angle and hematocrit was better at higher frequencies. Because of this, the c 2 constant approaches zero and H eSt can reliably be estimated using only the 10 kHz and 20 kHz data. Use of lower frequencies, however, allows for slight improvements in the strip-to-strip variability of the H est function.
• the present invention therefore may be used to estimate hematocrit using only AC phase angle measurements preferably made at at least one AC frequency, more preferably made at at least two AC frequencies, and most preferably made at at least four AC frequencies. Because the hematocrit can be determined using only the AC response data, and we know from Figure 20 that admittance is linearly related to hematocrit and temperature, we can now determine the temperature of the sample under analysis using only the AC response as follows:
• b 0 , b 1; b 2 and b 3 are constants. It will be appreciated that the estimation of hematocrit and temperature from the AC response data may be made with more or fewer frequency measurements, and at different frequencies than those chosen for this example. The particular frequencies that produce the most robust results will be determined by test strip geometries and dimensions.
• the present invention therefore may be used to estimate test sample temperature using only AC response measurements preferably made at at least one AC frequency, more preferably made at at least two AC frequencies, and most preferably made at at least four AC frequencies.
• the direct measurement of the temperature of the sample under test is a great improvement over prior art methods for estimating the temperature of the sample.
• a thermistor is placed in the test meter near where the test strip is inserted into the meter. Because the thermistor is measuring a temperature remote from the actual sample, it is at best only a rough approximation of the true sample temperature. Furthermore, if the sample temperature is changing (for example due to evaporation), then the thermal inertia of the test meter and even the thermistor itself will prevent the meter-mounted thermistor from accurately reflecting the true temperature of the sample under test.
• the temperature estimation of the present invention is derived from measurements made within the sample under test (i.e. within the reaction zone in which the sample under test reacts with the reagent), thereby eliminating any error introduced by the sample being remote from the measuring location.
• the temperature estimation of the present invention is made using data that was collected very close in time to the glucose measurement data that will be corrected using the temperature estimation, thereby further improving accuracy.
• the uncompensated DC current response versus known glucose concentration is plotted in Figure 22 for all 125 combinations of glucose, temperature and hematocrit (the AC measurements were ignored when plotting this data).
• the data exhibits huge variation with respect to hematocrit and temperature.
• the accuracy of the DC glucose response can be greatly improved by combining the estimated hematocrit, temperature and DC response to correct for the hematocrit and temperature interference in the DC response as follows:
• Equation 13 (ao + + hct 2 He S t 2 + tauiT ⁇ t + tau 2 T est ) (Equation 13) + (a 1 DC)(l + hct 3 He St + hct 4 H es t 2 )(l + tau 3 T est + tau T est )
• the constants in Equation 13 can be determined using regression analysis, as is known in the art.
• the present invention therefore allows one to estimate hematocrit by using the AC phase angle response (Equation 11).
• the estimated hematocrit and the measured AC admittance can be used to determine the estimated temperature (Equation 12).
• the estimated hematocrit and estimated temperature can be used with the measured DC response to obtain the predicted glucose concentration (Equation 13).
• the excitation profile illustrated in Figure 24 was utilized in order to decrease the Total Test Time. As described above with respect to Example 5, it was determined that the phase angle at 20 kHz and at 10 kHz were most closely correlated with the hematocrit estimation. It was therefore decided to limit the AC portion of the excitation to these two frequencies in Example 6 in order to decrease the Total Test Time. In order to make further reductions in Total Test Time, the 10 kHz AC excitation was applied simultaneously with the DC signal (i.e. an AC signal with a DC offset), the theory being that this combined mode would allow for the collection of simultaneous results for DC current, AC phase and AC admittance, providing the fastest possible results.
• the DC signal i.e. an AC signal with a DC offset
• the 20 kHz signal was applied for 0.9 seconds. Thereafter, the 10 kHz and DC signals were applied simultaneously for 1.0 second after a 0J second interval.
• 49 spiked venous blood samples representing seven glucose levels and seven hematocrit levels were tested.
• the correlation coefficient r 2 between the DC current and the blood hematocrit was then examined at three DC measurement times: 1J seconds, 1.5 seconds and 1.9 seconds after sample application. These correlations are plotted versus hematocrit level in Figure 25. All of these results are comparable, although the correlation is generally poorest at 1J seconds and generally best at 1.5 seconds. The minimum correlation coefficient, however, exceeds 0.99.
• Figure 26 illustrates the phase angle at 20 kHz plotted against hematocrit levels.
• Figure 27 illustrates the DC current response versus glucose level for all measured hematocrit levels as the read time is varied between 1J seconds, 1.5 seconds and 1.9 seconds. Not surprisingly, the DC current at 1J seconds is greater than the DC current at 1.5 seconds, which is greater than the DC current at 1.9 seconds. Those skilled in the art will recognise that the hematocrit level has a large effect on the DC current, particularly at high glucose concentrations.
• the accuracy of the DC glucose response can be greatly improved by compensating for the interference caused by hematocrit as follows:
• Equation 15 does not include temperature compensation terms since temperature variation was not included in the experiment of this Example 6, it can be reasonably inferred from previous examples that a Test term could be included using the 10 kHz and 20 kHz admittance values in combination with the He St term. Because the hematocrit can be reliably estimated using only the 20 kHz phase angle measurement data, the hematocrit compensated predicted glucose response can be determined using only this phase angle information and the measured DC response.
• the compensated DC response versus glucose level for only the DC read at 1J seconds (representing a 1J second Total Test Time) is illustrated in Figure 28. The data shows an overall r 2 correlation of 0.9947 with a 1J second Total Test Time.
• Example 7 Use of AC Phase Angle (o Detect an Abused Sensor
• Cottrell Failsafe Ratio CFR
• the Cottrell response of the biosensor in the Confidence system can be given by:
• NCFR Cottrell failsafe ratio
• a Current Sum Failsafe can be devised that places a check on the Cottrell response of the sensor by summing all of the acquired currents during sensor measurement. When the final current is acquired, it is multiplied by two constants
• MCFR Modified Cottrell Failsafe Ratio
• the preferred embodiment performs the following check when there are two DC blocks:
• the NCFR (and MCFR) is correlated with hematocrit.
• the AC phase angle is also correlated with hematocrit. It follows then, that the AC phase angle and the NCFR are correlated with one another. This relationship holds only if the sensor is unabused. The correlation degrades for an abused sensor. It is therefore possible to design an equation to analyze the measured phase angle data to produce a failsafe calculation that will indicate if an abused sensor is being used. In the preferred embodiment, it was chosen to use the difference between the phase angles measured at two separate frequencies in order to make the test more robust to errors caused by parasitic resistance, etc.
• each of these solutions each incorporate one or the other electrode of the measurement pair in communication with either the upstream or the downstream indicator electrodes to assess the presence of a sufficient volume of sample to avoid biased test results.
• failure modes persist wherein the devices remain prone to misinterpretation of sample sufficiency.
• the present inventors have determined that such erroneous conclusions are related primarily to the distances between a downstream member of a measurement electrode pair (co- planar or opposing geometries) and the dose detection electrode, in combination with the diversity of non-uniform flow fronts.
• a sample traversing the capillary fill space having an aberrant (uneven) flow front can close the circuit between a measurement electrode and an indicator electrode and erroneously advise the system that sufficient sample is present to avoid a biased measurement result.
• Many factors employed in the composition and/or fabrication of the test strip capillary fill spaces influence such irregular flow front behavior. These factors include:
• Another problem with prior art dose sufficiency methodologies determined by the present inventors relates to the use of one or the other of the available measurement electrodes in electrical communication with an upstream or downstream dose detection electrode.
• the stoichiometry of the measurement zone (the area above or between the measurement electrodes) is perturbed during the dose detect/dose sufficiency test cycle prior to making a measurement of the analyte of interest residing in the measurement zone.
• sample matrices vary radically in make-up, the fill properties of these samples also vary, resulting in timing differences between sample types.
• Such erratic timing routines act as an additional source of imprecision and expanded total system error metrics.
• Example 8 Determination of Fluid Flow Fron( Behavior in a Capillary Fill Space
• Test fixtures comprising two sheets of clear polycarbonate sheets joined together with double-sided adhesive tape were used, where the capillary fill space was formed by cutting a channel in the double- sided tape.
• Use of the polycarbonate upper and lower sheets allowed the flow fronts of the sample to be videotaped as it flowed through the capillary fill space.
• test devices were laminated using laser cut 1mm thick Lexan® polycarbonate sheets (obtained from Cadillac Plastics Ltd., Westlea, Swindon SN5 7EX, United Kingdom).
• Lexan® polycarbonate sheets obtained from Cadillac Plastics Ltd., Westlea, Swindon SN5 7EX, United Kingdom.
• the top and bottom polycarbonate sheets were coupled together using double-sided adhesive tapes (#200MP High).
• the capillary channels were defined by laser cutting the required width openings into the double-sided tape. Tape thicknesses of 0.05 ⁇ m, 0J25 ⁇ m, and 0.225 ⁇ m were used to give the required channel heights. The dimensions of the capillary spaces of the test devices are tabulated in FIG. 31.
• the top and bottom polycarbonate parts were laminated together with the laser cut adhesive tapes using a custom-built jig to ensure reproducible fabrication. For each test device, a fluid receptor region defining the entrance to the capillary channel was formed by an opening pre-cut into the upper polycarbonate sheet and adhesive tape components.
• channel widths 0.5mm, 1.00mm, 1.5mm, 2.00mm, 3.00mm, and 4.00mm were fabricated.
• the capillary channel length for all devices was 50mm.
• Twenty-eight (28) of each of the eighteen (18) device types were constructed.
• the assembled devices were plasma treated by Weidman Plastics Technology of Dortmund, Germany. The following plasma treatment conditions were used:
• Microwave plasma processor 400 Microwave plasma processor 400
• the plasma-treated devices were stored at 2 - 8°C when not in use. The devices were allowed to equilibrate to room temperature for one (1) hour minimum before use. Each of the test devices was dosed with a fixed volume of venous blood having a hematocrit value of 45%. Flow and flow front behavior was captured on videotape for later analysis. It was determined that the relative dimensions of the capillary fill channel determined the flow front behavior. Devices to the left of the dashed line in FIG.
• FIGs. 32A-C The problems associated with a concave flow front in a capillary fill space are illustrated in FIGs. 32A-C.
• the test strip includes a working electrode 3200, a reference electrode 3202, and a downstream dose sufficiency electrode 3204 that works in conjunction with one of the measurement electrodes 3200 or 3202.
• FIGs. 32A-C illustrate that a sample flow front exhibiting a concave shape can also cause biased measurement results. In each drawing, the direction of sample travel is shown by the arrow. In FIG.
• FIG. 32A illustrates the portions of the sample adjacent to the capillary walls have reached the dose sufficiency electrode 3204, thereby electrically completing the DC circuit between this electrode and one of the measurement electrode pair that is being monitored by the test meter in order to make the dose sufficiency determination.
• the test meter will conclude that there is sufficient sample to make a measurement at this time, the sample clearly has barely reached the reference electrode 3202 and any measurement results obtained at this time will be highly biased.
• FIG. 32B illustrates the situation where the dose sufficiency electrode 3204 has been contacted (indicating that the measurement should be started), but the reference electrode 3202 is only partially covered by the sample.
• the present invention solves the stoichiometric problems associated with the prior art designs pairing the dose sufficiency electrode with one of the measurement electrodes when making the dose sufficiency determination. As shown in FIG.
• the present invention comprehends a test strip having an independent pair of dose sufficiency electrodes positioned downstream from the measurement electrodes.
• the test strip is indicated generally as 3300, and includes a measurement electrode pair consisting of a counter electrode 3302 and a working electrode 3304.
• the electrodes may be formed upon any suitable substrate in a multilayer test strip configuration as is known in the art and described hereinabove.
• the multilayer configuration of the test strip provides for the formation of a capillary fill space 3306, also as known in the art.
• a dose sufficiency working electrode 3308 and a dose sufficiency counter electrode 3310 are formed within the capillary fill space 3306, and downstream (relative to the direction of sample flow) from the measurement electrodes 3302 and 3304.
• the test meter will continuously check for a conduction path between the dose sufficiency electrodes 3308 and 3310 in order to determine when the sample has migrated to this region of the capillary fill space. Once the sample has reached this level, the test meter may be programmed to conclude that the measurement electrodes are covered with sample and the sample measurement sequence may be begun.
• test strip 3300 is also desirable for judging dose sufficiency when the capillary fill space is designed to produce samples that exhibit a convex flow front while filling the capillary fill space 3306, as illustrated in FIG. 34A.
• the measurement zone above the measurement electrodes 3302 and 3304 is covered with sample when the convex flow front reaches the dose sufficiency electrode pair 3308,3310.
• the test strip design 3300 may not, however, produce ideal results if the capillary fill space 3306 allows the sample to exhibit a concave flow front while filling, as shown in FIG. 34B.
• the peripheral edges of the concave flow front reach the dose sufficiency electrodes 3308,3310 before the measurement zone has been completely covered with sample.
• the dose sufficiency electrodes 3308,3310 will indicate sample sufficiency as soon as they are both touched by the edges of the flow front.
• the dose sufficiency electrode design shown in the test strip of FIG. 33 works best when the sample filling the capillary space 3306 exhibits a convex flow front. It will be appreciated that the dose sufficiency electrodes 3308,3310 have their longest axis within the capillary fill space 3306 oriented perpendicular to the longitudinal axis of the capillary fill space 3306. Such electrodes are referred to herein as "perpendicular dose sufficiency electrodes.” An alternative dose sufficiency electrode arrangement is illustrated in FIGs. 35A-B. As shown in FIG.
• the present invention also comprehends a test strip having an independent pair of dose sufficiency electrodes positioned downstream from the measurement electrodes, where the dose sufficiency electrodes have their longest axis within the capillary fill space oriented parallel to the longitudinal axis of the capillary fill space.
• Such electrodes are referred to herein as "parallel dose sufficiency electrodes.”
• the test strip in FIG. 35 is indicated generally as 3500, and includes a measurement electrode pair consisting of a counter electrode 3502 and a working electrode 3504.
• the electrodes may be formed upon any suitable substrate in a multilayer test strip configuration as is known in the art and described hereinabove.
• the multilayer configuration of the test strip provides for the formation of a capillary fill space 3506, also as known in the art.
• a dose sufficiency working electrode 3508 and a dose sufficiency counter electrode 3510 are formed within the capillary fill space 3506, and downstream (relative to the direction of sample flow) from the measurement electrodes 3502 and 3504 .
• the test meter will continuously check for a conduction path between the dose sufficiency electrodes 3508 and 3510 in order to determine when the sample has migrated to this region of the capillary fill space. Once the sample has reached this level, the test meter may be programmed to conclude that the measurement electrodes are covered with sample and the sample measurement sequence may be begun.
• the dose sufficiency electrodes 3508,3510 display significant edge effects, wherein the excitation signal traverses the gap between the electrodes only when the electrode edges along the gap are covered with the sample fluid.
• the test strip 3500 is illustrated in enlarged size in FIG. 36 (with only the electrode portions lying within the capillary fill space 3506 and the strip-to-meter electrode contact pads visible).
• the majority of the signal travels from one electrode edge to the edge of the other electrode (when the edges are covered with sample), rather than from the upper flat surface of one electrode to the upper flat surface of the other electrode.
• edge-to-edge electrical communication are illustrated schematically as the electric field lines 3602 in FIG. 36.
• Higher AC frequencies produce the best edge-only sensitivity from the dose sufficiency electrodes.
• a 9 mV rms (+/- 12.7 mV peak-to-peak) excitation signal of lOkHz is used to excite one of the dose sufficiency electrodes.
• the gap width GW between the edges of the dose sufficiency electrodes 3508,3510 is preferably 100-300 ⁇ m, more preferably 150- 260 ⁇ m, and most preferably 255 ⁇ m.
• a smaller gap width GW increases the amount of signal transmitted between dose sufficiency electrodes whose edges are at least partially covered by sample; however, the capacitance of the signal transmission path increases with decreasing gap width GW.
• An advantage of the parallel dose sufficiency electrode design of FIGs. 35 and 36, when used with AC excitation, is that there is substantially no electrical communication between the electrodes until the sample covers at least a portion of the edges along the electrode gap. Therefore, a sample exhibiting the concave flow front of FIG. 35 A, where the illustrated sample is touching both of the dose sufficiency electrodes 3508,3510 but is not touching the electrode edges along the gap, will not produce any significant electrical communication between the dose sufficiency electrodes.
• the test meter will therefore not form a conclusion of dose sufficiency until the sample has actually bridged the dose sufficiency electrodes between the electrode edges along the gap. This will happen only after the rearmost portion of the concave flow front has reached the dose sufficiency electrodes 3508,3510, at which point the sample has completely covered the measurement zone over the measurement electrodes. As can be seen in FIG. 35B, convex sample flow fronts will activate the dose sufficiency electrodes 3508,3510 as soon as the flow front reaches the dose sufficiency electrodes (at which point the sample has completely covered the measurement zone over the measurement electrodes). Another advantage to the parallel dose sufficiency electrodes illustrated in FIGs.
• 35 and 36 is that the amount of signal transmitted between the electrodes is proportional to the amount of the gap edges that is covered by the sample.
• an appropriate threshold value in the test meter By employing an appropriate threshold value in the test meter, a conclusion of dose sufficiency can therefore be withheld until the sample has covered a predetermined portion of the dose sufficiency electrode gap edge.
• an analysis of the dose sufficiency signal will allow the test meter to record the percentage of fill of the capillary fill space for each measurement made by the test meter, if desired. While the electrode geometry itself demonstrates an advantage over previous embodiments in terms of detecting an adequate sample, particularly in the case of a convex flow front, it was found that further improvement is achieved in the use of AC responses over DC responses for sample detection.
• DC responses have the problems of being sensitive to variations in, for example, temperature, hematocrit and the analyte (glucose for example).
• AC responses at sufficiently high frequency can be made robust to the variation in the analyte concentration.
• the AC response generated at sufficiently high frequencies in such capillary fill devices is primarily limited by the amount of the parallel gap between the electrode edges which is filled by the sample. Thus, for a convex flow front, little or no AC response (in this case admittance) is perceived until the trough of the flow front actually intrudes within the parallel edges of the sample sufficiency electrodes.
• the senor can be made more or less sensitive as is deemed advantageous, with a higher threshold for admittance requiring more of the parallel gap to be filled before test initiation.
• a further limitation of existing devices is the inability of the electrode geometry to discern the amount of time needed to fill the capillary space of the sensor. This limitation is caused by having interdependence of the dose sufficiency electrode and the measurement electrodes. This is a further advantage of independent dose sufficiency electrodes. In the preferred embodiment a signal is first applied across the measurement electrodes prior to dosing.
• the potential is immediately switched off and a second signal is applied across the dose sufficiency electrodes during which time the system both looks for a response to the signal (indicating electrode coverage) and marks the duration between the first event (when a response is observed at the measurement electrodes) and the second event (when a response is observed at the dose sufficiency electrodes).
• a threshold within which acceptable results may be obtained and outside of which a failsafe is triggered, preventing a response or at a minimum warning the user of potential inaccuracy.
• the amount of time lag between dosing and detection of a sufficient sample that is considered allowable is dependent upon the particular sensor design and chemistry.
• an independent pair of dose detection electrodes may be added upstream from the measurement electrodes in order to detect when the sample is first applied to the sensor.
• a DC signal could be used for detection in either or both of the above events
• the preferred embodiment uses an AC signal at sufficiently high frequency to avoid unnecessarily perturbing the electrochemical response at the measurement electrodes and to provide robust detection with respect to flow front irregularities.

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