WO2012114706A1 - 生体試料測定装置 - Google Patents
生体試料測定装置 Download PDFInfo
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- WO2012114706A1 WO2012114706A1 PCT/JP2012/001096 JP2012001096W WO2012114706A1 WO 2012114706 A1 WO2012114706 A1 WO 2012114706A1 JP 2012001096 W JP2012001096 W JP 2012001096W WO 2012114706 A1 WO2012114706 A1 WO 2012114706A1
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- biological sample
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- 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
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
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- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12M—APPARATUS FOR ENZYMOLOGY OR MICROBIOLOGY; APPARATUS FOR CULTURING MICROORGANISMS FOR PRODUCING BIOMASS, FOR GROWING CELLS OR FOR OBTAINING FERMENTATION OR METABOLIC PRODUCTS, i.e. BIOREACTORS OR FERMENTERS
- C12M1/00—Apparatus for enzymology or microbiology
- C12M1/34—Measuring or testing with condition measuring or sensing means, e.g. colony counters
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- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
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- 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
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- 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
- G01N27/416—Systems
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- 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
- G01N27/416—Systems
- G01N27/417—Systems using cells, i.e. more than one cell and probes with solid electrolytes
- G01N27/4175—Calibrating or checking the analyser
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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
- G01N33/483—Physical analysis of biological material
- G01N33/487—Physical analysis of biological material of liquid biological material
- G01N33/49—Blood
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- G—PHYSICS
- G16—INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR SPECIFIC APPLICATION FIELDS
- G16B—BIOINFORMATICS, i.e. INFORMATION AND COMMUNICATION TECHNOLOGY [ICT] SPECIALLY ADAPTED FOR GENETIC OR PROTEIN-RELATED DATA PROCESSING IN COMPUTATIONAL MOLECULAR BIOLOGY
- G16B40/00—ICT specially adapted for biostatistics; ICT specially adapted for bioinformatics-related machine learning or data mining, e.g. knowledge discovery or pattern finding
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
- H01J49/00—Particle spectrometers or separator tubes
- H01J49/0027—Methods for using particle spectrometers
- H01J49/0036—Step by step routines describing the handling of the data generated during a measurement
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- G—PHYSICS
- G06—COMPUTING; CALCULATING OR COUNTING
- G06F—ELECTRIC DIGITAL DATA PROCESSING
- G06F2218/00—Aspects of pattern recognition specially adapted for signal processing
Definitions
- the present invention relates to a biological sample measuring apparatus that measures information (such as blood glucose level) of a biological sample spotted on a sensor, for example.
- a biological sample measurement device that measures biological data, such as a blood glucose level measurement device that measures blood glucose levels.
- a biological sample measurement device is equipped with a biological sample measurement sensor that introduces a biological sample spotted at the tip suction port using capillary action into the capillary.
- biological sample information such as a blood glucose level, is measured by applying a predetermined voltage with respect to the electrode of a biological sample measuring sensor, and measuring the output value from an output electrode.
- Patent Document 1 discloses an electrochemical sensor that informs re-testing when the amount of a liquid sample containing an analysis object is insufficient.
- the conventional sensor has the following problems. That is, in the sensor disclosed in the above publication, the sub-element of the detection electrode is provided upstream of the working electrode in the flow path of the biological sample, and electrochemical conduction occurs between the working electrode and the sub-element, resulting in a current value. When the value exceeds an arbitrary threshold value, it is determined that a sufficient current has passed to satisfy an effective test for measuring the concentration of a biological sample, and measurement is started.
- the spotting monitoring time until the current value exceeds an arbitrary threshold is short (for example, 1 to 5 seconds), and if the current value does not exceed the arbitrary threshold during the spotting monitoring time, It was judged as an error immediately. In this case, it is necessary to discard the sensor, puncture again, collect blood, and measure using a new sensor.
- the blood component when measuring using blood as a biological sample, the blood component is infiltrated while the blood plasma component soaks into the reagent even though the blood volume is insufficient for accurate measurement. It may reach the electrode to be detected (soaking phenomenon). Even in this case, since the current value exceeds a predetermined threshold, it may be erroneously determined that the blood is sufficiently filled.
- An object of the present invention is to accurately detect the degree of introduction of a biological sample into the capillary of the sensor without being affected by the wraparound phenomenon or the penetration phenomenon even when the amount of the biological sample spotted on the sensor is small.
- An object of the present invention is to provide a possible biological sample measuring device.
- the biological sample measurement device is equipped with a biological sample measurement sensor that introduces a spotted biological sample into the capillary by capillary action and reacts the reagent provided in the capillary with the biological sample,
- a biological sample measurement device that measures a biological sample, and includes a mounting unit, a voltage application unit, and a control unit.
- the mounting part is mounted with a biological sample measurement sensor.
- the voltage application unit applies a measurement voltage to a plurality of electrodes arranged along the capillary in the biological sample measurement sensor.
- the control unit eliminates the influence of the intrusion of the biological sample due to the wraparound phenomenon or the penetration phenomenon at the end of the capillary based on the output result measured by applying the voltage from the voltage application unit to the electrode. The degree of introduction of the biological sample in is detected.
- the biological sample spotted on the biological sample measurement sensor is introduced into the capillary by capillary action, and the reagent provided in the capillary is reacted with the biological sample.
- a biological sample measurement device that measures a biological sample by applying a voltage
- the biological sample at the end of the capillary due to the wraparound phenomenon is determined based on the output result of the voltage applied to a plurality of electrodes provided along the capillary.
- the influence (introduction level) of the biological sample is detected in the capillary by eliminating the influence of the penetration and the influence of the plasma component due to the penetration phenomenon.
- the “wraparound phenomenon” means that the biological sample is located at the back of the capillary along both ends in the width direction in a small introduction gap (capillary) provided for introducing the biological sample into the biological sample measurement sensor. This refers to a phenomenon that penetrates to the part.
- the “immersion phenomenon” refers to a phenomenon in which blood plasma components reach a detection electrode while being immersed in a reagent when blood is used as a biological sample.
- the plasma component in the blood is reagent. If it reaches the detection electrode while soaking in the blood, it may be erroneously detected if blood is filled in the capillary.
- a voltage is applied to a plurality of electrodes arranged along the capillary. Based on the applied output result, it is possible to accurately determine the position in the capillary where the biological sample has been introduced by distinguishing the output result when the wraparound phenomenon or penetration phenomenon occurs and the output result during normal filling. Can be detected.
- the characteristic of the graph showing the time passage and the output result is that the sneaking phenomenon or the soaking phenomenon occurs. For example, based on the difference in the slope of the graph and the magnitude of the output value, whether it is the output result when the wraparound phenomenon or dip phenomenon occurs, or during normal filling Can be detected.
- the biological sample measuring device is the biological sample measuring device according to the first invention, and the control unit detects a sufficient amount of the biological sample in the capillary as a result of detecting the degree of introduction of the biological sample. After determining that the sample is not filled, the peak of the output result exceeding a predetermined threshold is detected to detect additional spotting of the biological sample.
- the peak of the output value of the voltage applied to the electrode is detected after it is determined that the biological sample is not sufficiently filled as a result of detecting the degree of introduction of the biological sample in the capillary of the biological sample measurement sensor described above. If this is the case, this is detected as having additional spotting.
- the additional spotting means that when the amount of spotting is insufficient when the biological sample is spotted for the first time, the biological sample measuring sensor is noticed again by the notification from the biological sample measuring device or the measurer. This means adding a biological sample.
- the apparatus performs subsequent additional spotting. By detecting it, it is possible to automatically detect the transition to a measurable state.
- a biological sample measurement device is the biological sample measurement device according to the first or second invention, wherein the electrode is composed of a first electrode disposed at the innermost part of the capillary and a first electrode. And a second electrode disposed on the entrance side of the capillary and in a region where the reagent is provided. Based on a function related to the slope of the graph indicating the output result obtained by applying a voltage between the first and second electrodes, the control unit determines whether the capillary is in a normal filling state, a wraparound phenomenon, or a penetration phenomenon occurrence state. judge.
- the value of the output result in the period after the lapse of the predetermined time when the most characteristic difference appears between the normal filling and the wraparound phenomenon or the soaking phenomenon occurs For example, the change rate of the output result can be detected with high accuracy by raising it to the nth power.
- a biological sample measurement device is the biological sample measurement device according to the first or second aspect of the invention, wherein the electrode is composed of a first electrode disposed at the innermost part of the capillary and a first electrode.
- a second electrode disposed in a region where the reagent is provided on the inlet side of the capillary, a third electrode disposed between the first and second electrodes and closer to the capillary inlet side than the second electrode, have.
- the controller Based on a function relating to the slope of the graph showing the output result obtained by alternately applying a voltage between the first and third electrodes and between the second and first electrodes at predetermined time intervals, the controller is normal in the capillary It is determined whether it is a filling state, a sneaking phenomenon or a soaking phenomenon.
- the voltage was obtained by alternately applying a voltage between the first electrode and the third electrode at the innermost part of the capillary and between the second electrode of the reagent part and the first electrode at predetermined time intervals.
- a function relating to the slope of the graph indicating the output result it is determined whether the output value obtained by applying the voltage is due to the normal filling state of the biological sample, or due to the wraparound phenomenon or the soaking phenomenon occurrence state.
- the value of the output result in the period after the lapse of the predetermined time when the most characteristic difference appears between the normal filling and the wraparound phenomenon or the soaking phenomenon occurs For example, the change rate of the output result can be detected with high accuracy by raising it to the nth power.
- a biological sample measurement device is the biological sample measurement device according to the first or second aspect of the present invention, wherein the electrode comprises a first electrode disposed at the innermost part of the capillary and a first electrode.
- a second electrode disposed in a region where the reagent is provided on the inlet side of the capillary, a third electrode disposed between the first and second electrodes and closer to the capillary inlet side than the second electrode, have.
- the control unit determines whether the capillary is in a normal filling state, a wraparound phenomenon, or a penetration phenomenon occurrence state. judge.
- the value of the output result in the period after the lapse of the predetermined time when the most characteristic difference appears between the normal filling and the wraparound phenomenon or the soaking phenomenon occurs For example, the change rate of the output result can be detected with high accuracy by raising it to the nth power. Thereby, it is possible to accurately detect whether the biological sample is filled up to the innermost part of the capillary while preventing erroneous detection due to the influence of the wraparound phenomenon and the penetration phenomenon.
- a biological sample measurement device is the biological sample measurement device according to any one of the first to fifth aspects, further comprising a display unit that displays information relating to the biological sample. Based on the detection result of the biological sample introduction degree, the control unit causes the display unit to display a display for prompting additional spotting of the biological sample.
- the display for prompting the patient or measurer to add additional biological samples is performed.
- the patient or the like immediately recognizes that the biological sample that was initially spotted is insufficient and performs additional spotting, thereby performing accurate measurement without wasting the biological sample measurement sensor. be able to.
- a biological sample measurement device is the biological sample measurement device according to any one of the first to fifth inventions, and further includes a display unit for displaying information relating to the biological sample.
- the control unit causes the display unit to display a measurement error display based on the detection result of the biological sample introduction degree.
- a measurement error indicating that the measurement is impossible due to the amount of the biological sample spotted is insufficient for the patient or measurer.
- the patient or the like immediately recognizes that the biological sample that was initially spotted is insufficient and performs additional spotting, thereby performing accurate measurement without wasting the biological sample measurement sensor. be able to.
- the invention's effect According to the biological sample measurement device of the present invention, even when the amount of biological sample spotted on the biological sample measurement sensor is small and the biological sample is not sufficiently filled in the capillary, the wraparound phenomenon and the penetration phenomenon It is possible to prevent erroneous detection of the biological sample by the above and accurately detect to which position in the capillary the biological sample is filled.
- FIG. 2 is a control block diagram of the biological sample measurement device of FIG. 1.
- the flowchart which shows the flow of the autostart control by the biological sample measuring apparatus of FIG. (A) is a graph which shows the output result with respect to the passage of time when the biological sample is spotted on the sensor by a normal amount in the biological sample measuring device of FIG.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- (C) is a graph which shows the output result with respect to time passage at the time of additional spotting.
- (D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X; The flowchart which shows the flow of the autostart control by the biological sample measuring device which concerns on other embodiment of this invention.
- (A) is the graph which shows the output result with respect to time passage when the biological sample is spotted by the normal quantity by the sensor in the biological sample measuring device concerning other embodiments of the present invention.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- (C) is a graph which shows the output result with respect to time passage at the time of additional spotting.
- (D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X; The flowchart which shows the flow of the autostart control by the biological sample measuring device which concerns on other embodiment of this invention.
- (A) is a graph which shows the output result with respect to time passage when the biological sample is spotted by the sensor by the normal quantity in the biological sample measuring device concerning other embodiments of the present invention.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- (C) is a graph which shows the output result with respect to time passage at the time of additional spotting.
- (D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X;
- (A) is a graph which shows the output result with respect to time passage when the biological sample is spotted by the sensor by the normal quantity in the biological sample measuring device concerning other embodiments of the present invention.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- (C) is a graph which shows the output result with respect to time passage at the time of additional spotting.
- D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X;
- (A) is a graph which shows the output result with respect to time passage when the biological sample is spotted by the sensor by the normal quantity in the biological sample measuring device concerning other embodiments of the present invention.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- C is a graph which shows the output result with respect to time passage at the time of additional spotting.
- (D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X;
- (A) is a graph which shows the output result with respect to time passage when the biological sample is spotted by the sensor by the normal quantity in the biological sample measuring device concerning other embodiments of the present invention.
- (B) is a graph showing an output result with respect to the passage of time when a biological sample runs short and a wraparound phenomenon or a soaking phenomenon occurs.
- (C) is a graph which shows the output result with respect to time passage at the time of additional spotting.
- (D) to (f) are graphs showing the relationship between the passage of time corresponding to (a) to (c) and the value of X;
- (A) is a disassembled perspective view of a biological sample measurement sensor used in a biological sample measurement device according to still another embodiment of the present invention.
- (B) is the sectional side view.
- (C) is a plan view thereof.
- (A) is a disassembled perspective view of a biological sample measurement sensor used in a biological sample measurement device according to still another embodiment of the present invention.
- (B) is the sectional side view.
- (C) is a plan view thereof.
- (A) is a disassembled perspective view of a biological sample measurement sensor used in a biological sample measurement device according to still another embodiment of the present invention.
- (B) is the sectional side view.
- FIG. 1 A biological sample measuring apparatus according to an embodiment of the present invention will be described below with reference to FIGS. 1 to 6 (f).
- the biological sample measurement apparatus according to the present embodiment is provided at the lower end of the main body case 1, the display unit 2 and the operation buttons 33 for operation provided on the surface of the main body case 1. And a mounting portion 4 for the biological sample measurement sensor 3.
- FIGS. 2A to 2C the biological sample measurement sensor 3 is formed by laminating a substrate 5, a spacer 6, and a cover 7 so as to be integrated.
- FIG. 2A is a developed perspective view of the biological sample measurement sensor 3
- FIG. 2B is a cross-sectional view of the biological sample measurement sensor 3 viewed from the side
- FIG. The plan view of the sample measurement sensor 3 (however, the state without the cover 7 is shown) is shown.
- the substrate 5 is a plate-like member serving as a base of the biological sample measurement sensor 3, and an electrode (second electrode) 8a, an electrode (third electrode) 8b, and an electrode (first electrode) 8c are provided on the upper surface thereof. It has been.
- a reagent 10 that reacts with a biological sample such as blood is provided on the electrode 8a to 8c on the side where the biological sample is deposited.
- the spacer 6 is disposed so as to be sandwiched between the substrate 5 and the cover 7, and has a groove 11 at the end on the side where the biological sample is spotted. Then, by integrating the substrate 5, the spacer 6, and the cover 7, the groove 11 functions as a capillary that is a biological sample introduction path.
- the biological sample such as blood spotted on the biological sample measuring sensor 3 advances to the inside by the capillary phenomenon in the groove 11 functioning as a capillary.
- a reaction occurs between the reagent 10 and a specific component (for example, glucose in blood) included in the biological sample.
- a specific component for example, glucose in blood
- information related to a biological sample is measured based on this reaction value.
- the substrate 5 is longer than the spacer 6 and the cover 7 in the longitudinal direction, as shown in FIGS. 2 (a) to 2 (c).
- the electrodes 8a to 8c provided on the substrate 5 are exposed to the outside of the sensor at the end opposite to the spotted side of the biological sample.
- the biological sample measurement sensor 3 and the electric circuit in the main body case 1 can be electrically connected only by mounting the biological sample measurement sensor 3 on the mounting portion 4 of the main body case 1.
- the cover 7 has an air hole 7 a for promoting capillary action in the capillary at a position corresponding to the end on the back side of the groove 11 of the spacer 6.
- the air hole 7a is arranged on the back side (right side in FIG. 2) from the position on the biological sample measurement sensor 3 where the reagent 10 is placed.
- a biological sample such as blood spotted on the tip side (left side in FIG. 2) of the capillary can be smoothly introduced to the position of the reagent 10 by capillary action.
- the electrodes 8a to 8c are connected to a voltage application unit 12 and a current-voltage conversion unit 13 provided on the biological sample measurement device side in a state where the biological sample measurement sensor 3 is mounted (see FIG. 3).
- the biological sample measuring device of the present embodiment includes a mounting unit 4 to which the above-described biological sample measuring sensor 3 is mounted, a voltage applying unit 12, a reference, and a reference body.
- a voltage unit 12a, a current / voltage conversion unit 13, an A / D (analog / digital) conversion unit 18, a control unit 20, a memory unit 23, and a display unit 2 are provided.
- the display unit 2 displays various information such as a measurement value (for example, blood glucose level) of a biological sample, a message for prompting additional spotting to be described later, and a measurement error.
- the voltage application unit 12 is connected to the mounting unit 4 to which the biological sample measurement sensor 3 is mounted, and applies a predetermined voltage to the electrode of the biological sample measurement sensor 3.
- the reference voltage unit 12 a applies a reference voltage to a terminal that is a counter electrode part of the biological sample measurement sensor 3. Thereby, the voltage applied to both ends of the biological sample measurement sensor 3 is the difference between the voltage applied from the voltage application unit 12 and the voltage applied from the reference voltage unit 12a.
- the current-voltage conversion unit 13 is connected to the mounting unit 4 to which the biological sample measurement sensor 3 is mounted. As a result of applying a predetermined voltage from the voltage application unit 12 and the reference voltage unit 12a, the current-voltage conversion unit 13 The current value output from the output electrode is converted into a voltage value.
- the A / D converter 18 is connected to the output side of the current / voltage converter 12, receives a signal output from the current / voltage converter 12, and is connected to the controller 20.
- the control unit 20 controls the display unit 2, the voltage application unit 12, and the reference voltage unit 12 a with reference to an output value from the A / D conversion unit 18 and threshold data stored in the memory unit 23.
- the auto start control based on the threshold determination before the measurement start by the control unit 20 will be described in detail later.
- the memory unit 23 stores threshold data, measurement values, arithmetic expressions, and the like necessary for threshold determination described later, and necessary data is appropriately extracted by the control unit 20 and used.
- ⁇ Auto start control> In the biological sample measuring apparatus of the present embodiment, as shown in FIG. 4, a predetermined voltage is applied to the electrodes 8a to 8c arranged so as to be exposed in the capillary of the biological sample measuring sensor 3. Then, based on the output result, it is determined whether the biological sample spotted on the biological sample measurement sensor 3 is sufficiently filled in the capillary, and measurement is not started until the capillary is sufficiently filled. In this way, auto start control is performed.
- the biological sample measurement sensor 3 is provided with a plurality of electrodes 8a to 8c along the longitudinal direction of the capillary (groove 11).
- the electrode disposed at the portion where the reagent 10 is disposed is the A electrode
- the electrode 8c disposed at the innermost part of the capillary is the C electrode
- the electrode is disposed so as to sandwich the electrode 8a (A electrode).
- Reference numerals 8b and 8b denote E electrodes.
- a predetermined amount is provided between AC electrodes (electrodes 8a and 8c). Is applied to detect the state in which the biological sample is not sufficiently filled in the capillary of the biological sample measurement sensor 3, and the measurement is not automatically started until the biological sample is sufficiently filled. Perform auto start control.
- the output value is preferably a threshold voltage (10 to 50 mV. For example, Wait until it exceeds 15 mV).
- the electrode to which the voltage is applied is switched between the AC electrodes.
- the threshold value preferably a voltage of 10 to 50 mV, such as 20 mV
- glucose or the like Start measuring.
- the set value of the threshold value when executing the auto-start function is preferably changed according to the level of the environmental temperature at the time of measurement.
- the reaction between the biological sample and the reagent slows down, so that the threshold value of the output value of the voltage applied between the AE electrodes (voltage of 5 to 30 mV)
- the threshold value of the output value of the voltage applied between the AC electrodes for example, a voltage of 5 to 30 mV is preferable. For example, 10 mV may be used.
- step S1 a predetermined voltage V1 (preferably a voltage of 150 mV to 1.0 V, for example, 500 mV) is applied between the AC electrodes.
- the predetermined voltage V1 is a voltage applied to detect whether or not the biological sample is filled in the capillary.
- step S2 an output value (expressed as a voltage value after the output current is converted into a voltage) obtained by applying a voltage between the AC electrodes is a predetermined threshold V2 (a voltage of 1 to 30 mV is preferable).
- V2 a voltage of 1 to 30 mV is preferable.
- step S6 the control unit 20 displays a measurement error.
- the display unit 2 is controlled.
- a value X used for threshold determination is calculated in step S3. Specifically, an output value at a certain time T is A, and an output value B before the predetermined time (preferably within a range of 0.01 to 2 seconds. For example, 0.1 second). The calculated value X is calculated.
- the calculated value X is calculated by the following relational expression (1).
- X (A 4 / B 4 ⁇ 1) 4 (1) That is, here, the value X is calculated by further raising the value obtained by subtracting “1” from the ratio of the values obtained by raising the output current values A and B to the fourth power.
- the reason why the output current values A, B, etc. are raised to the fourth power is a threshold judgment for more accurately detecting whether or not the biological sample is sufficiently filled in the capillary. This is to improve the accuracy.
- FIG. 6A is a graph showing the relationship between the elapsed time and the output current value during normal spotting when a sufficient amount of biological sample is spotted on the sensor and the capillary is sufficiently filled.
- the above “sufficient amount” means an amount that causes a sufficient reaction for measurement and is sufficient to fill the biological sample to cover the entire working electrode inside the capillary. Although it depends on the size of the capillary volume and the arrangement of the working electrode and other detection electrodes in the capillary, it is preferable that 50% or more of the capillary volume is filled. More preferably, it may be 80% or more. For example, when the capillary volume is 0.6 ⁇ L, 0.5 ⁇ l or more is sufficient.
- FIG. 6B shows that an insufficient amount (for example, less than 0.5 ⁇ l) of a biological sample is spotted on the sensor and the capillary is not sufficiently filled, and a wraparound phenomenon or a penetration phenomenon occurs. It is the graph which showed the relationship between the time passage in the state which carried out, and an output electric current value.
- step S4 the value X calculated in step S3 is compared with a preset threshold value.
- the value X is equal to or greater than the threshold value, it is determined that a sufficient amount of the biological sample is filled in the capillary, and the measurement voltage is applied to the electrode to automatically start the measurement. Applied to 8a to 8c.
- the control part 20 controls the voltage application part 12 so that the voltage for starting a measurement automatically may be applied.
- step S4 if the value X is less than the threshold value in step S4, the capillary is not filled with a sufficient amount of the biological sample, and the detected current value causes the wraparound phenomenon or the penetration phenomenon. It is determined that the current value is accompanied, and the process proceeds to step S5.
- control part 20 controls the voltage application part 12 so that the voltage for automatically starting a measurement may not be applied accidentally.
- the control unit 20 controls the display unit 2 to receive a result of the threshold determination in step S3 and to display a message that prompts the patient to make additional spotting.
- the threshold value used at the time of threshold value determination is set according to the environmental temperature at the time of measurement. As a specific example, when the environmental temperature T is less than 20 ° C., the threshold is 0.2, and when the environmental temperature T is 20 ° C. or more and less than 30 ° C., the threshold is 0.5 and the environmental temperature T is When the temperature is 30 ° C. or higher, the threshold is set to 1.2. Then, the degree of introduction of the biological sample is determined by changing the threshold value according to the environmental temperature and comparing the value with the value X.
- the auto start control is performed with high accuracy regardless of the change in the environmental temperature. be able to.
- the temperature range (5 to 45 degrees) that can be measured by the biological sample measuring device of the present embodiment has been described as being divided into three cases, but the present invention is not limited to this. For example, it may be divided into two or less cases, or may be divided into four or more cases.
- step S5 when the patient additionally deposits a biological sample on the biological sample measurement sensor 3 by displaying a message prompting additional spotting, the capillary is filled with the biological sample at once and the reagent Since the reaction with 10 proceeds, as shown in FIG. 6C, the output current value rapidly increases and appears as a peak current.
- the filling state can be detected.
- the peak current may be detected using a threshold set for detecting the peak current.
- the threshold values in the graphs of FIGS. 6A and 6B described above indicate threshold values used in the conventional auto-start control.
- the output current value obtained as a result of the sample entering and gradually reacting with the reagent 10 is detected and the threshold value is exceeded (when 3 seconds elapses in FIG. 6B), the measurement is automatically started. .
- a measurement result lower than actual may be obtained.
- the biological sample measuring apparatus of this embodiment in order to accurately detect the degree of introduction of the biological sample in the capillary, numerical values A and B relating to the slopes of the graphs shown in FIGS. 6 (a) and 6 (b) are used.
- the value X is calculated by the used function (relational expression (1)), and as shown in FIGS. 6D and 6E, the threshold value is determined by comparing the value X with the threshold value.
- a display for prompting additional spotting (step S5) and detecting that there has been additional spotting. It has a function to do. This not only detects whether there is a sufficient amount of biological sample in the capillary for measurement, but also encourages it to be measurable by additional spotting while using the same sensor. Can do. As a result, the biological sample measurement sensor 3 does not need to be discarded because the amount of the biological sample deposited is insufficient at the time of the first spotting, and thus the biological sample measurement sensor 3 can be used effectively without being wasted.
- FIGS. 7 and 8 (a) to 8 (f) A biological sample measuring apparatus according to another embodiment of the present invention will be described below with reference to FIGS. 7 and 8 (a) to 8 (f).
- a difference between the electrodes (CE) between the first embodiment between the AC electrodes.
- the value X is calculated using another relational expression, and the auto-start control is performed. Therefore, in this embodiment, since the basic flow is the same as the flowchart shown in FIG. 5 described in the first embodiment, only different parts will be described below, and description of common parts will be omitted. .
- the electrode (first electrode) 8c disposed at the innermost part of the capillary, and between the electrodes 8a and 8c and between the electrodes 8a, Between the electrodes (third electrodes) 8b and 8b respectively arranged on the entrance side, and on the entrance side of the capillary with respect to the electrode 8c and in the region where the reagent 10 is provided (second electrode) ) A voltage is applied alternately between the electrode 8a and the electrode (first electrode) 8c every predetermined time, and auto-start control is performed.
- the control unit 20 performs a predetermined time interval (0.01) between the electrodes 8c and 8b (between CE electrodes) and between the electrodes 8a and 8c (between AC electrodes).
- the output obtained by applying a predetermined voltage preferably in the range of 150 mV to 1 V, for example, 500 mV
- a predetermined voltage preferably in the range of 150 mV to 1 V, for example, 500 mV
- a sufficient amount of biological sample is spotted on the biological sample measurement sensor 3 (see FIG. 8A) and an insufficient amount.
- the output current value with respect to the voltage applied between the CE electrodes at a certain time T is A, and the first predetermined time (in the range of 0.01 to 2 seconds).
- the output current value B with respect to the voltage applied between the CE electrodes before is set as the second predetermined time (in the range of 0.01 to 2 seconds) of the time T.
- the output current value A ′ with respect to the voltage applied between the AC electrodes before, and the first predetermined time (preferably in the range of 0.01 to 2 seconds. For example, 0 (2 seconds))
- the output current value B ′ with respect to the voltage previously applied between the AC electrodes is set, and the value X is calculated based on the following relational expression (2).
- step S11 a predetermined voltage is alternately alternately applied between the CE electrodes and between the AC electrodes (preferably in the range of 150 mV to 1 V. For example, 500 mV). Apply.
- Step S2 is common to the flowchart of FIG. 5 of the first embodiment.
- step S13 the value X is calculated based on the relational expression (2).
- step S14 the value X calculated in step S13 is compared with a preset threshold value.
- the value X is equal to or greater than the threshold value, it is determined that a sufficient amount of the biological sample is filled in the capillary, and the measurement voltage is applied to the electrode to automatically start the measurement. Applied to 8a to 8c.
- the control part 20 controls the voltage application part 12 so that the voltage for starting a measurement automatically may be applied.
- the control part 20 controls the voltage application part 12 so that the voltage for automatically starting a measurement may not be applied accidentally.
- the threshold used at the time of the threshold determination in step S14 is set according to the level of the environmental temperature at the time of measurement.
- the threshold value is 2
- the threshold value is 4
- the degree of introduction of the biological sample is determined by changing the threshold value according to the environmental temperature and comparing the value with the value X.
- the auto start control is performed with high accuracy regardless of the change in the environmental temperature.
- the temperature range (5 degrees to 45 degrees) that can be measured by the biological sample measuring device of the present embodiment has been described in three cases, but the present invention is not limited to this. For example, it may be divided into two or less cases, or may be divided into four or more cases.
- step S5 when the patient additionally deposits a biological sample on the biological sample measurement sensor 3 by displaying a message prompting additional spotting, the capillary is filled with the biological sample at once and the reagent Since the reaction with 10 proceeds, as shown in FIG. 8C, the output current value rapidly rises around the elapsed time of 4 seconds and appears as a peak current.
- the peak current may be detected using a threshold set for detecting the peak current.
- the threshold values in the graphs of FIGS. 8A and 8B described above indicate the threshold values used in the conventional auto-start control.
- the threshold values in the graphs of FIGS. 8A and 8B described above indicate the threshold values used in the conventional auto-start control.
- the output current value obtained as a result of the sample entering and gradually reacting with the reagent 10 is detected and the threshold value is exceeded, the measurement is automatically started (see FIG. 8B).
- a measurement result lower than actual may be obtained.
- the value X is calculated using the expression (2)), and the threshold value is determined by comparing the value X with the threshold value as shown in FIGS. 8 (d) and 8 (e).
- FIGS. 9 and 10 (a) to 10 (f) A biological sample measuring apparatus according to still another embodiment of the present invention will be described below with reference to FIGS. 9 and 10 (a) to 10 (f).
- the value X is calculated using another relational expression based on the result of applying a voltage between the electrodes), and the auto-start control is performed. Therefore, in this embodiment, since the basic flow is the same as the flowchart shown in FIG. 5 described in the first embodiment, only different parts will be described below, and description of common parts will be omitted. .
- the electrode (first electrode) 8c disposed at the innermost part of the capillary, and between the electrodes 8a and 8c and between the electrodes 8a, A voltage is applied between the electrodes (third electrodes) 8b and 8b arranged on the entrance side, and auto-start control is performed.
- control unit 20 preferably has a predetermined voltage (in the range of 150 mV to 1 V) between the electrodes 8c and 8b (between the CE electrodes) as shown in step S21 in FIG. ) Is applied to determine whether the capillary is in a normal filling state, a wraparound phenomenon, or a soaking phenomenon occurrence state based on a graph (see FIGS. 10 (a) and 10 (b)) showing an output result obtained. .
- a sufficient amount of biological sample is spotted on the biological sample measurement sensor 3 (see FIG. 10A) and an insufficient amount.
- the output current value with respect to the voltage applied between the CE electrodes at a certain time T is A, and the predetermined time (preferably in the range of 0.01 to 2 seconds). (For example, 0.1 seconds.)
- the output current value B with respect to the voltage applied between the CE electrodes before is calculated as a value X based on the following relational expression (3).
- X (A 4 / B 4 ⁇ 1) 4 (3) That is, here, the value X is calculated by further raising the value obtained by subtracting “1” from the ratio of the values obtained by raising the output current values A and B to the fourth power.
- a predetermined voltage (preferably in the range of 150 mV to 1 V. For example, 500 mV) is applied between the CE electrodes.
- Step S2 is common to the flowchart of FIG. 5 of the first embodiment.
- step S23 the value X is calculated based on the relational expression (3).
- step S24 the value X calculated in step S23 is compared with a preset threshold value.
- the value X is equal to or greater than the threshold value, it is determined that a sufficient amount of the biological sample is filled in the capillary, and the measurement voltage is applied to the electrode to automatically start the measurement. Applied to 8a to 8c.
- the control part 20 controls the voltage application part 12 so that the voltage for starting a measurement automatically may be applied.
- the control part 20 controls the voltage application part 12 so that the voltage for automatically starting a measurement may not be applied accidentally.
- the threshold value used at the time of the threshold value determination of step S24 is set according to the level of the environmental temperature at the time of measurement.
- the threshold value is set according to the level of the environmental temperature at the time of measurement.
- the threshold value is set to 2 respectively. Then, the degree of introduction of the biological sample is determined by changing the threshold value according to the environmental temperature and comparing the value with the value X.
- the auto start control is performed with high accuracy regardless of the change in the environmental temperature.
- the temperature range (5 degrees to 45 degrees) that can be measured by the biological sample measuring device of the present embodiment has been described in three cases, but the present invention is not limited to this. For example, it may be divided into two or less cases, or may be divided into four or more cases.
- step S5 when the patient additionally deposits a biological sample on the biological sample measurement sensor 3 by displaying a message prompting additional spotting, the capillary is filled with the biological sample at once and the reagent Since the reaction with No. 10 proceeds, the output current value rapidly rises around the elapsed time of 7 seconds and appears as a peak current as shown in FIG.
- such a peak current is detected by detecting that the value X calculated by the relational expression (3) exceeds the threshold, and thus The filling state in the capillary after the additional spotting can be detected.
- the peak current may be detected using a threshold set for detecting the peak current.
- the threshold values in the graphs of FIGS. 10A and 10B described above indicate the threshold values used in the conventional auto-start control.
- the detection electrode detects the output current value obtained as a result of the sample entering and gradually reacting with the reagent 10 to exceed the threshold, or the plasma component in the blood soaks into the reagent 10 due to the soaking phenomenon. If the output value obtained as a result of the gradual reaction exceeds the threshold value (about 3 seconds in FIG. 10B), the measurement is automatically started.
- a measurement result lower than actual may be obtained.
- the value X is calculated by the relational expression (3), and as shown in FIGS. 10D and 10E, the value X is compared with the threshold value to determine the threshold value.
- the threshold value may be determined by calculating the value X shown in FIGS. 11D to 11F.
- the output current value with respect to the voltage applied between the EC electrodes at a certain time T is A, and the first predetermined time (preferably in the range of 0.01 to 2 seconds. For example, 0.2 seconds. .)
- the output current value B with respect to the voltage previously applied between the EC electrodes is the second predetermined time of the time T (preferably in the range of 0.01 to 2 seconds, for example, 0.1 second).
- the output current value A ′ with respect to the voltage previously applied between the AC electrodes, and between the AC electrodes before the first predetermined time preferably in the range of 0.01 to 2 seconds, for example, 0.2 seconds).
- the value X is compared with the threshold value and the threshold value is determined.
- the calculated value X is compared with a predetermined threshold value. , X exceeds a threshold value, it is determined that the biological sample is normally filled in the capillary and measurement is automatically started.
- FIG. 11 (e) when X is equal to or less than the threshold value, it is determined that the wraparound phenomenon or the penetration phenomenon occurs, and as shown in FIGS. 11 (c) and 11 (f). Wait until additional spotting (peak current value) is detected.
- the influence of the wraparound phenomenon and the penetration phenomenon is eliminated compared with the conventional threshold determination in which the measurement result and the threshold value are simply compared. It is possible to more accurately detect whether or not the biological sample is sufficiently filled with (the degree of introduction of the biological sample). As a result, it is possible to avoid the start of measurement automatically until there is an additional spotting and a sufficient amount of biological sample is filled in the capillary, and to perform highly accurate autostart control. .
- a normal voltage indicating an output current value obtained with the passage of time as a result of applying a predetermined voltage (preferably in the range of 150 mV to 1 V. For example, 500 mV) to the AC electrode is shown.
- a predetermined voltage preferably in the range of 150 mV to 1 V. For example, 500 mV
- the threshold value may be determined by calculating the value X shown in 12 (d) and FIG. 12 (e).
- the output current value at a certain time T is A
- the output current values B and A before the predetermined time are used.
- the output current value before a predetermined time (preferably within a range of 0.01 to 2 seconds, for example, 0.5 second) is set to a predetermined time A ′ and B (within a range of 0.01 to 2 seconds). (For example, 0.5 seconds.)
- the calculated value X is compared with a predetermined threshold value, and X exceeds the threshold value. In this case, it is determined that the biological sample is normally filled in the capillary and measurement is automatically started. On the other hand, if X is less than or equal to the threshold value, it is determined that a wraparound phenomenon or a soaking phenomenon has occurred, and an additional spotting (peak current value) is calculated as shown in FIGS. 12 (c) and 12 (f). Wait for detection.
- the threshold value may be set to “5”.
- the influence of the wraparound phenomenon and the penetration phenomenon is eliminated compared with the conventional threshold determination in which the measurement result and the threshold value are simply compared. It is possible to more accurately detect whether or not the biological sample is sufficiently filled with (the degree of introduction of the biological sample). As a result, it is possible to avoid the start of measurement automatically until there is an additional spotting and a sufficient amount of biological sample is filled in the capillary, and to perform highly accurate autostart control. .
- FIGS. 13 (a) to 13 (c) show output current values obtained over time as a result of applying a predetermined voltage (for example, 500 mV) to the AC electrode.
- the threshold value may be determined by calculating a value X shown in FIGS. 13 (d) and 13 (e).
- the slope of the graph is calculated by taking two points before and after the waveform of the graph, and this is set as the value X.
- the calculated value X is compared with a predetermined threshold, and X exceeds the threshold. In this case, it is determined that the biological sample is normally filled in the capillary and measurement is automatically started. On the other hand, when X is less than or equal to the threshold value, it is determined that the wraparound phenomenon or the penetration phenomenon has occurred, and the additional spotting (peak current value) is calculated as shown in FIGS. 13 (c) and 13 (f). Wait for detection.
- the threshold value may be set to “50”.
- the influence of the wraparound phenomenon and the penetration phenomenon is eliminated compared with the conventional threshold determination in which the measurement result and the threshold value are simply compared. It is possible to more accurately detect whether or not the biological sample is sufficiently filled with (the degree of introduction of the biological sample). As a result, it is possible to avoid the start of measurement automatically until there is an additional spotting and a sufficient amount of biological sample is filled in the capillary, and to perform highly accurate autostart control. .
- step S3 shown in FIG. 5 in order to improve the accuracy of threshold determination, an example in which the value X used for threshold determination is calculated by raising each value of output current and the like to the fourth power has been described. .
- the present invention is not limited to this.
- the calculation method of the value X is not limited to the fourth power.
- the value n is set in a function using numerical values A, B, etc. so that the output value calculation system is most improved. You may make it improve the precision of threshold determination by riding.
- the electrode (second electrode) 8a, the electrode (third electrode) 8b, and the electrode (first electrode) are formed on the upper surface of the substrate 5.
- An example in which 8c is provided has been described.
- the present invention is not limited to this.
- the electrode (first electrode) 8 c is not substantially provided on the bonding surface side of the substrate 5, but is almost centered on the bonding surface side of the cover 7. It may be provided near the portion.
- the connecting terminal 4 in contact with the electrode 8 c provided on the bonding surface of the cover 7, which is provided in the mounting portion 4 on the biological sample measuring device side. Further, the terminals that contact the electrodes 8a and 8b provided on the substrate 5 side contact downward from above, and the terminals that contact the electrode 8c provided on the cover 7 side contact upward from below. To do. Therefore, in the portion of the substrate 5 facing the electrode 8c provided on the cover 7 side and the portion of the cover 7 facing the electrodes 8a and 8b provided on the substrate 5 side, as shown in FIG. Notches are respectively formed, and a space for receiving a connection terminal on the apparatus side is secured.
- the electrode 8c provided on the cover 7 side is provided in the innermost part of the capillary similarly to the electrode arrangement configuration of the first embodiment. This prevents false detection of a biological sample due to a wraparound phenomenon or a penetration phenomenon even when the amount of biological sample spotted on the biological sample measurement sensor is small and the biological sample is not sufficiently filled in the capillary. Thus, it is possible to obtain the same effect as the configuration of the first embodiment in which it is possible to accurately detect to which position in the capillary the biological sample is filled.
- the electrode (second electrode) 8a, the electrode (third electrode) 8b, and the electrode (first electrode) 8c are formed on the upper surface of the substrate 5.
- the electrode (third electrode) 8b is substantially the entire surface on the bonding surface side of the cover 7 instead of being provided on the bonding surface side of the substrate 5. May be provided.
- connection terminal in contact with the electrode 8b provided on the bonding surface of the cover 7 in the reverse direction. Further, the terminals that contact the electrodes 8a and 8c provided on the substrate 5 side contact from the top downward, and the terminals that contact the electrode 8b provided on the cover 7 side contact from the bottom upward. To do. Therefore, in the portion of the substrate 5 facing the electrode 8b provided on the cover 7 side and the portion of the cover 7 facing the electrodes 8a and 8c provided on the substrate 5 side, as shown in FIG. Notches are respectively formed, and a space for receiving a connection terminal on the apparatus side is secured.
- the electrode 8b provided on the cover 7 side is provided over the entire surface of the capillary portion as in the electrode arrangement configuration of the first embodiment. This prevents false detection of a biological sample due to a wraparound phenomenon or a penetration phenomenon even when the amount of biological sample spotted on the biological sample measurement sensor is small and the biological sample is not sufficiently filled in the capillary. Thus, it is possible to obtain the same effect as the configuration of the first embodiment in which it is possible to accurately detect to which position in the capillary the biological sample is filled.
- FIGS. 18 (a) to 18 (c) a biological sample measurement sensor 103 in which a capillary is formed along a direction intersecting the longitudinal direction and a biological sample can be spotted from both sides of the side surface. It may be.
- a capillary is formed along the width direction by the two spacers 106 and 106 sandwiched between the substrate 105 and the cover 107, and the reagent 110 is provided along the capillary.
- an electrode (second electrode) 108a provided substantially at the center of the substrate 105, and electrodes (third electrodes) provided on both sides of the electrode 108a, respectively. Electrodes) 108b and 108b and electrodes (first electrodes) 108c and 108c provided outside the electrodes 108b and 108b are provided.
- a predetermined voltage is alternately applied between the upper two electrodes 8b and 8c and the lower two electrodes 8b and 8c shown in FIG.
- the side on which the threshold output value (current or voltage) is obtained can be detected as the side on which the biological sample is supplied.
- the biological sample is measured using the electrode 8c disposed on the back side in the direction in which the biological sample flows out of the two electrodes 8c and 8c. be able to.
- Embodiment 1 in which it is possible to accurately detect the position in the capillary where the biological sample is filled by preventing erroneous detection of the biological sample due to the wraparound phenomenon or the penetration phenomenon even if the biological sample is not present. The same effect can be obtained.
- the biological sample measuring apparatus of the present invention accurately detects the degree of introduction of the biological sample into the capillary of the sensor without being affected by the wraparound phenomenon or the penetration phenomenon even when the amount of spotted biological sample on the sensor is small.
- the present invention is widely applicable to biological sample measuring devices that measure biological information such as blood glucose levels.
Abstract
Description
このような生体試料測定装置には、毛細管現象を利用して先端吸引口に点着した生体試料をキャピラリ内部に導入する生体試料測定センサが装着される。そして、生体試料測定装置では、生体試料測定センサの電極に対して所定の電圧を印加して出力電極からの出力値を測定することで、血糖値等の生体試料情報を測定する。
すなわち、上記公報に開示されたセンサでは、生体試料の流路において検知電極のサブエレメントを作用電極よりも上流側に設け、作用電極とサブエレメントとの間で電気化学的導通が起こって電流値が任意の閾値を超えると、生体試料の濃度測定の有効な試験を成り立たせるのに十分な電流が流れたと判定し、測定を開始するように構成されている。
これにより、キャピラリ最奥部まで生体試料が充填されているかを、回り込み現象や浸み込み現象の影響による誤検出を防止して正確に検出することができる。
これにより、患者等は最初に点着した生体試料が不足していたことをすぐに認識して追加点着を行うことで、生体試料測定センサを無駄にすることなく、正確な測定を実施することができる。
これにより、患者等は最初に点着した生体試料が不足していたことをすぐに認識して追加点着を行うことで、生体試料測定センサを無駄にすることなく、正確な測定を実施することができる。
本発明に係る生体試料測定装置によれば、生体試料測定センサに点着された生体試料の量が少なく、キャピラリ内において生体試料が十分に充填されていない場合でも、回り込み現象や浸み込み現象による生体試料の誤検知を防止して、キャピラリ内におけるどの位置まで生体試料が充填されているかを正確に検出することができる。
本発明の一実施形態に係る生体試料測定装置について、図1~図6(f)を用いて説明すれば以下の通りである。
[生体試料測定装置の構成]
本実施形態に係る生体試料測定装置は、図1に示すように、本体ケース1と、その表面に設けられた表示部2および操作用の操作ボタン33と、本体ケース1の下端に設けられた生体試料測定センサ3の装着部4と、を備えている。
生体試料測定センサ3は、図2(a)~図2(c)に示すように、基板5とスペーサ6とカバー7とを積層させて一体化されている。ここで、図2(a)は、生体試料測定センサ3の展開斜視図、図2(b)は、生体試料測定センサ3を側面から見た場合の断面図、図2(c)は、生体試料測定センサ3の平面図(ただし、カバー7がない状態を示す。)をそれぞれ示している。
電極8a~8cにおける生体試料の点着側には、血液等の生体試料と反応する試薬10が設けられている。
スペーサ6は、基板5とカバー7との間に挟まれるように配置されており、生体試料が点着される側の端部に溝11を有している。そして、基板5とスペーサ6とカバー7とを一体化することで、溝11の部分が生体試料の導入路であるキャピラリとして機能する。
空気孔7aは、図2(b)に示すように、生体試料測定センサ3における試薬10が載置された位置よりも奥側(図2では右側))に配置されている。これにより、キャピラリの先端側(図2では左側)に点着された血液等の生体試料を、毛細管現象によって試薬10の位置までをスムーズに導入することができる。
電極8a~8cは、生体試料測定センサ3が装着された状態において、生体試料測定装置側に設けられた電圧印加部12、電流電圧変換部13に接続される(図3参照)。
本実施形態の生体試料測定装置は、図3の制御ブロック図に示すように、本体ケース1内に、上述した生体試料測定センサ3が装着される装着部4と、電圧印加部12と、基準電圧部12aと、電流電圧変換部13と、A/D(アナログ/デジタル)変換部18と、制御部20と、メモリ部23と、表示部2と、を備えている。
電圧印加部12は、生体試料測定センサ3が装着される装着部4に接続されており、生体試料測定センサ3の電極に対して所定の電圧を印加する。
A/D変換部18は、電流電圧変換部12の出力側に接続されており、電流電圧変換部12から出力された信号を受信するとともに、制御部20に接続されている。
メモリ部23は、後述する閾値判定を行う際に必要な閾値データ、測定値、演算式等を保存しており、制御部20によって適宜必要なデータが取り出されて使用される。
本実施形態の生体試料測定装置では、図4に示すように、生体試料測定センサ3のキャピラリ内に露出するように配置された電極8a~8cに対して所定の電圧を印加する。そして、その出力結果に基づいて、生体試料測定センサ3に点着された生体試料がキャピラリ内に十分に充填されているか否かを判定し、十分に充填された状態になるまで測定を開始しないように、オートスタート制御を実施する。
具体的には、まず、ステップS1において、AC電極間に所定の電圧V1(150mV~1.0Vの電圧が好ましい。例えば、500mV)が印加される。なお、この所定の電圧V1は、生体試料がキャピラリ内に充填されているか否かを検出するために印加される電圧である。
なお、ここで説明する出力値(電流・電圧変換した後の電圧値:mV)=電流値(μA)×30(kΩ:抵抗)とする。
X=(A4/B4-1)4 ・・・・・(1)
すなわち、ここでは、出力電流値A,Bを4乗した値の比から“1”を引いた値をさらに4乗して値Xを算出している。
図6(a)は、十分な量の生体試料がセンサに点着されてキャピラリ内が十分に充填された通常点着時における時間経過と出力電流値との関係を示したグラフである。
なお、閾値判定時に用いられる閾値は、測定時の環境温度の高低に応じて設定されることが好ましい。具体的な例としては、環境温度Tが20℃未満の場合には、閾値は0.2、環境温度Tが20℃以上30度未満の場合には、閾値は0.5、環境温度Tが30℃以上である場合には、閾値は1.2にそれぞれ設定される。そして、環境温度によって閾値を変更して上記値Xと比較することにより、生体試料の導入度合いを判定する。
つまり、この従来の閾値設定だけでオートスタート制御を実施した場合には、キャピラリ内が生体試料によって十分に充填されていない場合でも、回り込み現象や浸み込み現象によってキャピラリの端部に沿って生体試料が浸入して試薬10と徐々に反応した結果得られる出力電流値を検出して閾値を超えてしまう(図6(b)の3秒経過時)と、自動的に測定が開始されてしまう。このような不十分な量の生体試料に対して測定用の電圧を印加して測定を実施した場合には、実際よりも低い測定結果が得られるおそれがある。
これにより、単に、測定に十分な量の生体試料がキャピラリ内にあるか否かを検出するだけでなく、同じセンサを用いたままでも、追加点着によって測定可能な状態になるように促すことができる。この結果、最初の点着時に生体試料の点着量が不足したために生体試料測定センサ3を廃棄する必要がないため、生体試料測定センサ3を無駄にせずに有効に使用することができる。
本発明の他の実施形態に係る生体試料測定装置について、図7および図8(a)~図8(f)を用いて説明すれば以下の通りである。
本実施形態では、上述した実施形態1で用いた生体試料測定装置と同じ構成の装置を用いて、血糖値等の測定開始前に、実施形態1(AC電極間)とは異なる電極間(CE電極間、AC電極間)に電圧を印加した結果に基づいて別の関係式を用いて値Xを算出し、オートスタート制御を実施している。よって、本実施形態では、上述した実施形態1において説明した図5に示すフローチャートと基本的な流れは同じであるため、以下では異なる部分だけを説明することとし、共通する部分の説明は省略する。
すなわち、ここでは、出力電流値AとA’,BとB’を乗算した値から “1”を引いた値を4乗して値Xを算出している。
なお、上記関係式(2)において、(A×A’)と(B×B’)の比から“1”を引いた数値を4乗している理由は、上記実施形態1の関係式(1)と同様に、キャピラリ内に生体試料が十分に充填されているか否かをより正確に検出するための閾値判定の精度を向上させるためである。
ステップS2については、上記実施形態1の図5のフローチャートと共通である。
そして、ステップS13では、上記関係式(2)に基づいて、値Xが算出される。
ここで、ステップS14の閾値判定時に用いられる閾値は、測定時の環境温度の高低に応じて設定されることが好ましい。具体例としては、環境温度Tが20℃未満の場合には、閾値は2、環境温度Tが20℃以上30℃未満の場合には、閾値は4、環境温度Tが30℃以上である場合には、閾値は8にそれぞれ設定される。そして、環境温度によって閾値を変更して上記値Xと比較することにより、生体試料の導入度合いを判定する。
なお、ここでは、本実施形態の生体試料測定装置の測定可能な温度範囲(5度~45度)を3つに場合分けして説明したが、本発明はこれに限定されるものではない。例えば、2つ以下に場合分けされてもよいし、4つ以上に細かく場合分けされてもよい。
つまり、この従来の閾値設定だけでオートスタート制御を実施した場合には、キャピラリ内が生体試料によって十分に充填されていない場合でも、回り込み現象や浸み込み現象によってキャピラリの端部に沿って生体試料が浸入して試薬10と徐々に反応した結果得られる出力電流値を検出して閾値を超えてしまうと、自動的に測定が開始されてしまう(図8(b)参照)。このような不十分な量の生体試料に対して測定用の電圧を印加して測定を実施した場合には、実際よりも低い測定結果が得られるおそれがある。
本発明のさらに他の実施形態に係る生体試料測定装置について、図9および図10(a)~図10(f)を用いて説明すれば以下の通りである。
本実施形態では、上述した実施形態1で用いた生体試料測定装置と同じ構成の装置を用いて、血糖値等の測定開始前に、実施形態1(AC電極間)とは異なる電極間(CE電極間)に電圧を印加した結果に基づいて別の関係式を用いて値Xを算出し、オートスタート制御を実施している。よって、本実施形態では、上述した実施形態1において説明した図5に示すフローチャートと基本的な流れは同じであるため、以下では異なる部分だけを説明することとし、共通する部分の説明は省略する。
X=(A4/B4-1)4 ・・・・・(3)
すなわち、ここでは、出力電流値A,Bを4乗した値の比から“1”を引いた値をさらに4乗して値Xを算出している。
本実施形態では、図9のフローチャートに示すように、まず、ステップS21において、CE電極間へ所定の電圧(150mV~1Vの範囲であることが好ましい。例えば、500mV。)を印加する。
そして、ステップS23では、上記関係式(3)に基づいて、値Xが算出される。
次に、ステップS24では、ステップS23において算出された値Xを、予め設定された閾値と比較する。ここで、値Xが閾値以上である場合には、キャピラリ内には十分な量の生体試料が充填されているものと判断して、自動的に測定を開始するために測定用の電圧を電極8a~8cに印加する。
なお、ステップS24の閾値判定時に用いられる閾値は、測定時の環境温度の高低に応じて設定されることが好ましい。具体例としては、環境温度Tが20℃未満の場合には、閾値は0.3、環境温度Tが20℃以上30℃未満の場合には、閾値は1、環境温度Tが30℃以上である場合には、閾値は2にそれぞれ設定される。そして、環境温度によって閾値を変更して上記値Xと比較することにより、生体試料の導入度合いを判定する。
なお、ここでは、本実施形態の生体試料測定装置の測定可能な温度範囲(5度~45度)を3つに場合分けして説明したが、本発明はこれに限定されるものではない。例えば、2つ以下に場合分けされてもよいし、4つ以上に細かく場合分けされてもよい。
つまり、この従来の閾値設定だけでオートスタート制御を実施した場合には、キャピラリ内が生体試料によって十分に充填されていない場合でも、回り込み現象や浸み込み現象によってキャピラリの端部に沿って生体試料が浸入して試薬10と徐々に反応した結果得られる出力電流値を検出して閾値を超えてしまう、あるいは、浸み込み現象によって血液中の血漿成分が試薬10に浸み込みながら検知電極まで到達し、徐々に反応した結果得られる出力値が閾値を超えてしまう(図10(b)の約3秒経過時)と、自動的に測定が開始されてしまう。このような不十分な量の生体試料に対して測定用の電圧を印加して測定を実施した場合には、実際よりも低い測定結果が得られるおそれがある。
以上、本発明の一実施形態について説明したが、本発明は上記実施形態に限定されるものではなく、発明の要旨を逸脱しない範囲で種々の変更が可能である。
(A)
上記実施形態1,2,3では、電極8a,8b,8cに対してそれぞれ電圧を印加してその出力電流値を時間経過ごとに示すグラフの傾き等に基づいて、通常充填時と回り込み現象や浸み込み現象発生時とを判別することで、回り込み現象や浸み込み現象の影響を排除しつつ、キャピラリ内における生体試料の位置を従来よりも高精度に検出する例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
X=(A×A’/B×B’-1)4 ・・・・・(2)
上記実施形態1,2,3では、電極8a,8b,8cに対してそれぞれ電圧を印加してその出力電流値を時間経過ごとに示すグラフの傾き等に基づいて、通常充填時と回り込み現象や浸み込み現象発生時とを判別することで、回り込み現象や浸み込み現象の影響を排除しつつ、キャピラリ内における生体試料の位置を従来よりも高精度に検出する例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
X=(A-B)/(A’-B’) ・・・・・(4)
これにより、上述した実施形態1~3と同様に、測定結果と閾値とを単純に比較する従来の閾値判定と比較して、回り込み現象や浸み込み現象の影響を排除することで、キャピラリ内に生体試料が十分に充填されているか否か(生体試料の導入度合い)をより正確に検出することができる。この結果、追加点着があってキャピラリ内に十分な量の生体試料が充填されるまで自動的に測定が開始されてしまうことを回避して、高精度なオートスタート制御を実施することができる。
上記実施形態1,2,3では、電極8a,8b,8cに対してそれぞれ電圧を印加してその出力電流値を時間経過ごとに示すグラフの傾き等に基づいて、通常充填時と回り込み現象や浸み込み現象発生時とを判別することで、回り込み現象や浸み込み現象の影響を排除しつつ、キャピラリ内における生体試料の位置を従来よりも高精度に検出する例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
具体的には、通常点着時のグラフ(図13(a)参照)と、回り込み現象や浸み込み現象発生時のグラフ(図13(b)参照)とで特性に明らかな差が有ることを利用して、グラフの波形の前後2点をとってグラフの傾きを算出して、これを値Xとすればよい。
これにより、上述した実施形態1~3と同様に、測定結果と閾値とを単純に比較する従来の閾値判定と比較して、回り込み現象や浸み込み現象の影響を排除することで、キャピラリ内に生体試料が十分に充填されているか否か(生体試料の導入度合い)をより正確に検出することができる。この結果、追加点着があってキャピラリ内に十分な量の生体試料が充填されるまで自動的に測定が開始されてしまうことを回避して、高精度なオートスタート制御を実施することができる。
上記実施形態では、図5に示すステップS3において、閾値判定の精度を向上させるために、出力電流等の値をそれぞれ4乗して閾値判定に使用する値Xを算出した例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
値Xの算出方法としては、4乗に限らず、例えば、これらの出力値の算出制度が最も向上するように、nの値を設定して数値A,B等を用いた関数において値をn乗することで、閾値判定の精度を向上させるようにしてもよい。
上記実施形態1では、図2(a)~図2(c)に示すように、基板5の上面に、電極(第2電極)8a、電極(第3電極)8b、電極(第1電極)8cが設けられている例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
例えば、図14(a)~図14(c)に示すように、電極(第1電極)8cについては、基板5の貼合せ面側に設ける代わりに、カバー7の貼合せ面側におけるほぼ中央部分付近に設けてもよい。
よって、カバー7側に設けられた電極8cに対向する基板5の部分、基板5側に設けられた電極8a,8bに対向するカバー7の部分には、図14(a)に示すように、それぞれ切欠きが形成されており、装置側の接続端子が入るスペースが確保されている。
上記実施形態では、図2(a)~図2(c)に示すように、基板5の上面に、電極(第2電極)8a、電極(第3電極)8b、電極(第1電極)8cが設けられている例を挙げて説明した。しかし、本発明はこれに限定されるものではない。
例えば、図16(a)~図16(c)に示すように、電極(第3電極)8bについては、基板5の貼合せ面側に設ける代わりに、カバー7の貼合せ面側におけるほぼ全面に設けてもよい。
よって、カバー7側に設けられた電極8bに対向する基板5の部分、基板5側に設けられた電極8a,8cに対向するカバー7の部分には、図16(a)に示すように、それぞれ切欠きが形成されており、装置側の接続端子が入るスペースが確保されている。
上記実施形態では、生体試料測定センサ3の長手方向に沿ってキャピラリが形成され、生体試料測定センサ3の長手方向における端部から血液等の生体試料が点着される構成を例として挙げて説明した。しかし、本発明はこれに限定されるものではない。
例えば、図18(a)~図18(c)に示すように、長手方向に交差する方向に沿ってキャピラリが形成されており側面における両側から生体試料の点着が可能な生体試料測定センサ103であってもよい。
2 表示部
3 生体試料測定センサ
4 装着部
5 基板
6 スペーサ
7 カバー
7a 空気孔
8a 電極(第2電極)
8b 電極(第3電極)
8c 電極(第1電極)
10 試薬
11 溝
12 電圧印加部
12a 基準電圧部
13 電流電圧変換部
18 A/D変換部
20 制御部
23 メモリ部
33 操作ボタン
103 生体試料測定センサ
105 基板
106 スペーサ
107 カバー
108a 電極(第2電極)
108b 電極(第3電極)
108c 電極(第1電極)
110 試薬
111 溝
Claims (7)
- 点着された生体試料を毛管現象によってキャピラリ内へ導入させ、前記キャピラリ内に設けられた試薬と前記生体試料とを反応させる生体試料測定センサが装着され、前記生体試料の測定を行う生体試料測定装置であって、
前記生体試料測定センサが装着される装着部と、
前記生体試料測定センサにおける前記キャピラリに沿って配置された複数の電極に測定するための電圧を印加する電圧印加部と、
前記電圧印加部から電圧が前記電極に印加されて測定された出力結果に基づいて、前記キャピラリの端部における回り込み現象または浸み込み現象による前記生体試料の浸入の影響を排除して、前記キャピラリ内における前記生体試料の導入度合いを検出する制御部と、
を備えている生体試料測定装置。 - 前記制御部は、前記生体試料の導入度合いを検出した結果、前記キャピラリ内に十分な量の前記生体試料が充填されていないと判断した後、前記出力結果が所定の閾値を超えたことを検出して前記生体試料の追加点着を検出する、
請求項1に記載の生体試料測定装置。 - 前記電極は、前記キャピラリの最奥部に配置された第1電極と、前記第1電極よりも前記キャピラリの入り口側であって前記試薬が設けられた領域に配置された第2電極と、を有しており、
前記制御部は、前記第1・第2電極間に電圧を印加して得られる出力結果を示すグラフの傾きに関する関数に基づいて、前記キャピラリ内が正常充填状態か回り込み現象または浸み込み現象の発生状態かを判定する、
請求項1または2に記載の生体試料測定装置。 - 前記電極は、前記キャピラリの最奥部に配置された第1電極と、前記第1電極よりも前記キャピラリの入り口側であって前記試薬が設けられた領域に配置された第2電極と、前記第1・第2電極の間および前記第2電極よりも前記キャピラリの入り口側に配置された第3電極と、を有しており、
前記制御部は、前記第1・第3電極間、前記第2・第1電極間に所定時間ごとに交互に電圧を印加して得られる出力結果を示すグラフの傾きに関する関数に基づいて、前記キャピラリ内が正常充填状態か、回り込み現象または浸み込み現象の発生状態かを判定する、
請求項1または2に記載の生体試料測定装置。 - 前記電極は、前記キャピラリの最奥部に配置された第1電極と、前記第1電極よりも前記キャピラリの入り口側であって前記試薬が設けられた領域に配置された第2電極と、前記第1・第2電極の間および前記第2電極よりも前記キャピラリの入り口側に配置された第3電極と、を有しており、
前記制御部は、前記第1・第3電極間に電圧を印加して得られる出力結果を示すグラフの傾きに関する関数に基づいて、前記キャピラリ内が正常充填状態か、回り込み現象や浸み込み現象の発生状態かを判定する、
請求項1または2に記載の生体試料測定装置。 - 前記生体試料に関する情報を表示する表示部をさらに備え、
前記制御部は、前記生体試料の導入度合いの検出結果に基づいて、前記生体試料の追加点着を促す表示を前記表示部に表示させる、
請求項1から5のいずれか1項に記載の生体試料測定装置。 - 前記生体試料に関する情報を表示する表示部をさらに備え、
前記制御部は、前記生体試料の導入度合いの検出結果に基づいて、測定エラーの表示を前記表示部に表示させる、
請求項1から5のいずれか1項に記載の生体試料測定装置。
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US14/927,470 Continuation US10241069B2 (en) | 2011-02-23 | 2015-10-30 | Biological sample measuring device |
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EP (1) | EP2679992B1 (ja) |
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US9297819B2 (en) * | 2011-07-22 | 2016-03-29 | Sysmex Corporation | Hematology analyzing system and analyzer |
WO2014057625A1 (ja) * | 2012-10-10 | 2014-04-17 | パナソニックヘルスケア株式会社 | 生体情報測定装置 |
JP6595122B2 (ja) | 2016-11-25 | 2019-10-23 | Phcホールディングス株式会社 | 生体試料の成分を測定する方法 |
Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2002057768A1 (en) * | 2001-01-17 | 2002-07-25 | Arkray, Inc. | Quantitative analyzing method and quantitative analyzer using sensor |
WO2002086483A1 (fr) * | 2001-04-16 | 2002-10-31 | Matsushita Electric Industrial Co., Ltd. | Biodetecteur |
JP2003004691A (ja) | 2001-05-21 | 2003-01-08 | Bayer Corp | 改良された電気化学的センサ |
JP2004245836A (ja) * | 2003-02-11 | 2004-09-02 | Bayer Healthcare Llc | 流体試料中の分析対象物の濃度を測定する方法 |
JP2007524826A (ja) * | 2003-06-20 | 2007-08-30 | エフ ホフマン−ラ ロッシュ アクチェン ゲゼルシャフト | 用量充足電極を使用する検体測定のためのシステムおよび方法 |
JP2008536139A (ja) * | 2005-04-15 | 2008-09-04 | アガマトリックス インコーポレーテッド | 電気化学的試験片内の部分的充填の決定 |
JP2010164584A (ja) * | 2010-04-27 | 2010-07-29 | Panasonic Corp | バイオセンサ、バイオセンサ用測定装置及び基質の定量方法 |
Family Cites Families (19)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7407811B2 (en) | 1997-12-22 | 2008-08-05 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using AC excitation |
US7494816B2 (en) | 1997-12-22 | 2009-02-24 | Roche Diagnostic Operations, Inc. | System and method for determining a temperature during analyte measurement |
US7390667B2 (en) | 1997-12-22 | 2008-06-24 | Roche Diagnostics Operations, Inc. | System and method for analyte measurement using AC phase angle measurements |
US6743635B2 (en) * | 2002-04-25 | 2004-06-01 | Home Diagnostics, Inc. | System and methods for blood glucose sensing |
CN100504371C (zh) * | 2002-07-25 | 2009-06-24 | 爱科来株式会社 | 试料分析方法和试料分析装置 |
US7488601B2 (en) | 2003-06-20 | 2009-02-10 | Roche Diagnostic Operations, Inc. | System and method for determining an abused sensor during analyte measurement |
US7597793B2 (en) | 2003-06-20 | 2009-10-06 | Roche Operations Ltd. | System and method for analyte measurement employing maximum dosing time delay |
EP3115777B1 (en) * | 2004-04-19 | 2020-01-08 | PHC Holdings Corporation | Method for measuring blood components |
GB0514728D0 (en) * | 2005-07-19 | 2005-08-24 | Hypoguard Ltd | Biosensor and method of manufacture |
KR20100103483A (ko) | 2007-10-31 | 2010-09-27 | 아크레이 가부시키가이샤 | 분석 용구, 분석 장치, 시료 부족의 검지 방법 및 시료 분석 방법 |
WO2009119118A1 (ja) * | 2008-03-27 | 2009-10-01 | パナソニック株式会社 | 試料測定装置、試料測定システム及び試料測定方法 |
JP2009250806A (ja) * | 2008-04-07 | 2009-10-29 | Panasonic Corp | バイオセンサシステム、センサチップおよび血液試料中の分析物濃度の測定方法 |
US8551320B2 (en) | 2008-06-09 | 2013-10-08 | Lifescan, Inc. | System and method for measuring an analyte in a sample |
EP3450969A1 (en) * | 2009-01-30 | 2019-03-06 | PHC Holdings Corporation | Sensor chip for measuring temperature of biological sample and concentration of analyte in the biological sample |
JP5428617B2 (ja) * | 2009-07-28 | 2014-02-26 | 富士通株式会社 | プロセッサ及び演算処理方法 |
CA2776332C (en) * | 2009-11-10 | 2018-05-01 | Bayer Healthcare Llc | Underfill recognition system for a biosensor |
IL209760A (en) * | 2009-12-11 | 2015-05-31 | Lifescan Scotland Ltd | A system and method for measuring filling is satisfactory |
JP4840520B2 (ja) | 2010-04-27 | 2011-12-21 | パナソニック株式会社 | バイオセンサ、バイオセンサ用測定装置及び基質の定量方法 |
CN104502426B (zh) * | 2010-06-07 | 2017-05-10 | 安晟信医疗科技控股公司 | 用于确定样品中的分析物浓度的方法 |
-
2012
- 2012-02-20 JP JP2013500879A patent/JP5728568B2/ja active Active
- 2012-02-20 US US13/982,747 patent/US9213015B2/en active Active
- 2012-02-20 WO PCT/JP2012/001096 patent/WO2012114706A1/ja active Application Filing
- 2012-02-20 EP EP12749390.6A patent/EP2679992B1/en active Active
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-
2015
- 2015-10-30 US US14/927,470 patent/US10241069B2/en active Active
Patent Citations (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2002057768A1 (en) * | 2001-01-17 | 2002-07-25 | Arkray, Inc. | Quantitative analyzing method and quantitative analyzer using sensor |
WO2002086483A1 (fr) * | 2001-04-16 | 2002-10-31 | Matsushita Electric Industrial Co., Ltd. | Biodetecteur |
JP2003004691A (ja) | 2001-05-21 | 2003-01-08 | Bayer Corp | 改良された電気化学的センサ |
JP2004245836A (ja) * | 2003-02-11 | 2004-09-02 | Bayer Healthcare Llc | 流体試料中の分析対象物の濃度を測定する方法 |
JP2007524826A (ja) * | 2003-06-20 | 2007-08-30 | エフ ホフマン−ラ ロッシュ アクチェン ゲゼルシャフト | 用量充足電極を使用する検体測定のためのシステムおよび方法 |
JP2008536139A (ja) * | 2005-04-15 | 2008-09-04 | アガマトリックス インコーポレーテッド | 電気化学的試験片内の部分的充填の決定 |
JP2010164584A (ja) * | 2010-04-27 | 2010-07-29 | Panasonic Corp | バイオセンサ、バイオセンサ用測定装置及び基質の定量方法 |
Non-Patent Citations (1)
Title |
---|
See also references of EP2679992A4 |
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EP2679992B1 (en) | 2019-10-23 |
CN103348239A (zh) | 2013-10-09 |
EP2679992A1 (en) | 2014-01-01 |
JPWO2012114706A1 (ja) | 2014-07-07 |
CN103348239B (zh) | 2015-09-30 |
US20160047776A1 (en) | 2016-02-18 |
US20130306474A1 (en) | 2013-11-21 |
EP2679992A4 (en) | 2016-05-11 |
US10241069B2 (en) | 2019-03-26 |
US9213015B2 (en) | 2015-12-15 |
JP5728568B2 (ja) | 2015-06-03 |
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