WO2003062812A1 - Analyzer having temperature sensor - Google Patents
Analyzer having temperature sensor Download PDFInfo
- Publication number
- WO2003062812A1 WO2003062812A1 PCT/JP2003/000225 JP0300225W WO03062812A1 WO 2003062812 A1 WO2003062812 A1 WO 2003062812A1 JP 0300225 W JP0300225 W JP 0300225W WO 03062812 A1 WO03062812 A1 WO 03062812A1
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- WIPO (PCT)
- Prior art keywords
- unit
- analyzer
- section
- detection unit
- calculation
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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
- G01K—MEASURING TEMPERATURE; MEASURING QUANTITY OF HEAT; THERMALLY-SENSITIVE ELEMENTS NOT OTHERWISE PROVIDED FOR
- G01K1/00—Details of thermometers not specially adapted for particular types of thermometer
- G01K1/16—Special arrangements for conducting heat from the object to the sensitive element
-
- 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
Definitions
- the present invention relates to an analyzer for mounting and using an analysis tool such as a Noo sensor and analyzing a sample based on information for calculation output from the analysis tool.
- a simple blood glucose measurement device sized to fit in the palm of the hand is widely used so that the blood glucose level can be easily measured at home or on the road.
- a blood sensor is measured by supplying a blood to the biosensor after attaching a biosensor configured as a single-use reaction field and disposable biosensor (for example, Japan). Japanese Patent Publication No. 8-10208).
- the amount of reductant (or oxidant) is generated according to the glucose concentration in the blood when it is transferred to the enzyme reaction field.
- the reductant or oxidant
- the electron transfer amount is measured as an oxidation current (or a reduction current) by a simple blood glucose level measuring device, and a blood glucose level is calculated based on the current value at that time. Since the reaction rate in an enzymatic reaction is relatively dependent, the amount of reductant (oxidized) produced depends not only on the glucose concentration in the blood but also on the reaction rate. Easily affected by For this reason, some simple blood glucose level measuring devices are configured to calculate the final measurement result after correcting for.
- This temperature measurement of ⁇ is performed, for example, by measuring the inside of a blood glucose concentration measuring device with a sensor incorporated in the blood glucose measuring device.
- the correction can also be performed by incorporating a sensor into the biosensor and incorporating information from the nosensor into the blood glucose measurement device.
- the method of measuring in a blood glucose measurement device does not necessarily reflect the reaction temperature because it does not measure the temperature (reaction temperature) of the biosensor.
- the temperature of the biosensor can be appropriately grasped, but a temperature sensor must be provided for each individual biosensor, which makes the biosensor expensive. Therefore, it is not practical to provide a biosensor with an SJt sensor in the biosensor for ⁇ : ⁇ . It is necessary to change not only the force and the no sensor but also the configuration of the simple blood glucose level measuring device.
- a simple blood glucose meter requires an input unit for taking in temperature information from a biosensor. Disclosure of the invention
- An analyzer provided by the present invention includes a mounting portion for mounting an analysis tool capable of outputting information for calculation, and a calculation for performing a calculation for analyzing a sample based on the information for calculation.
- An analyzer comprising: a detection unit that outputs information; and the detection unit is disposed in the mounting unit.
- the analyzer of the present invention is configured to further include a temperature correction unit that corrects a calculation result in the calculation unit based on the information.
- the detection unit has, for example, a parasite-type sensor. this:! ⁇ ,
- the detection unit is configured to include a light-transmitting unit having a insect-repelling surface for coming into contact with the sensor and causing the cap analysis tool to infest the insect.
- the cloud portion has, for example, a f i cloud conductivity of 0 ⁇ lOcal. It is formed of a material larger than C'cm 'sec). Preferably, the conductive part is formed of a material having a conductivity of greater than 0.15 cal / (° C-cm-sec).
- the display portion is preferably made of, for example, iron, copper, aluminum, an alloy mainly containing at least one of them, or ceramic.
- Insect-type sensor and sensor are sealed with a resin package May be arranged on the mounting portion.
- the worm-type sensor may be arranged so that when the analytical tool is attached to the mounting portion, the sensor directly inverts the analytical tool.
- the detection unit may be configured as having a non-contact type sensor.
- an analyzer having a reagent section as an analysis tool and an analyzer configured as a disposable can be used.
- the reagent section contains, for example, hydrogen.
- the enzyme for example, an enzyme having a catalytic action on an oxidation reaction of glucose is used.
- the detection section is arranged so as to be located in a region immediately below the reagent section, a region immediately above the reagent section, or a region in the vicinity thereof when the analysis tool is mounted on the mounting section.
- the mounting section is configured to include: an insertion section into which an end of the analysis tool is inserted; and a table section for mounting the analysis tool.
- the detecting device be disposed on the table.
- the table is formed, for example, so as to protrude to the side of the analyzer.
- a pressing part for pressing the analysis tool against the table part in the mounting part It is preferable to dispose a pressing part for pressing the analysis tool against the table part in the mounting part.
- the analysis tool a device equipped with an output unit for outputting the above information for calculation is used.
- the pressing unit forms a fiber on the output unit when the analysis tool is attached, and the information for force Q calculation is used.
- the apparatus be configured to have a function of inputting data to the analyzer.
- the pressing portion is configured as, for example, a panel made of a conductor.
- FIG. 1 is an overall plan view showing a state in which a biosensor is mounted on the analyzer according to the first embodiment of the present invention.
- FIG. 2 is a block diagram showing a schematic configuration of the analyzer shown in FIG.
- FIG. 3 is an overall perspective view showing an example of a biosensor.
- FIG. 4 is an exploded perspective view of the biosensor shown in FIG.
- FIG. 5 is a sectional view taken along line VV of FIG.
- FIG. 6 is a table showing an example of a list of correction coefficients.
- FIG. 7 is a cross-sectional view of a main part showing a state where a biosensor is mounted on the analyzer according to the second embodiment of the present invention, and corresponds to a cross section taken along line VV of FIG. . '
- FIG. 8 is a cross-sectional view of a main part showing a state where a biosensor is mounted on the analyzer according to the third embodiment of the present invention, and corresponds to a cross section taken along line VV of FIG. .
- FIG. 9 is a cross-sectional view of a main part showing a state where a biosensor is mounted on the analyzer according to the fourth embodiment of the present invention, and corresponds to a cross section along the line VV in FIG. You. BEST MODE FOR CARRYING OUT THE INVENTION
- the analyzer XI mounts the biosensor 2 on the mounting section 10 and measures the concentration of a specific component in the sample.
- the biosensor 2 has a cover 20, a spacer 21, and a substrate 22, as shown in FIGS.
- the cover 20 is provided with a hole 23.
- the spacer 21 is provided with a slit 24.
- the slit 24 is for defining the flow path 25 of the biosensor 2, has an open end 24 a, and communicates with the power hole 23. Therefore, the flow path 25 communicates with the outside via the open end 24a and the hole 23.
- the open end 24a of the cover 20 functions as a sample inlet, and the hole 23 functions as an air outlet. Therefore, while the sample is supplied from the open end (sample inlet) 24a, the air in the flow path 25 is discharged to the outside through the hole 23, while the sample is removed by the capillary action. Proceed along flow path 25 toward 23.
- a working electrode 26, a counter electrode 27, and a drug section 28 are provided on the upper surface 22a of the substrate 22.
- Most of the working electrode 26 and the pair 7 extend in the longitudinal direction of the fiber 22, and ends 26 a and 27 a extend in the lateral direction of the substrate 22. Therefore, action statement S26 and The counter electrode 27 has an L-shape as a whole.
- the ends 26 b and 27 b of the working electrode 26 and the counter electrode 27 are used to connect the terminal 17 of the analyzer XI to the fiber as shown in FIG.
- the reagent portion 28 is, for example, a solid, and connects the ends 26 a and 27 a of the working electrode 26 and the counter electrode 27 as well shown in FIGS. 4 and 5.
- the reagent part 28 is, for example, a relatively small amount of an oxidoreductase dispersed in a relatively large amount of an electron transfer substance.
- the electron mediator for example, a complex of iron or Ru is used.
- iron complexes that can be used for the ⁇ include, for example, a rheocyanidation force rim, and examples of the Ru complex include, for example, those having “H 3 as a ligand.
- the specific component is selected according to the type of elephant specific component such as, for example, glucose, cholesterol, and lactic acid. Cholesterol monoredehydrogenase, cholesterol noreoxidase, lactate dehydrogenase, lactate oxidase and the like.
- the analyzer ⁇ is a current value measurement unit 11, a detection unit 12, a calculation unit 13, a correction unit 14, and a display unit 15.
- a power supply 16 and a pair of terminals 17 (one terminal 17 is drawn in FIG. 5).
- the mounting section 10 is for holding the biosensor 2 and has an insertion section 18 and a table section 19.
- the inlet 18 is for inserting the end of the biosensor 2.
- the table section 19 is for mounting the biosensor 2 and protrudes to the side of the analyzer ⁇ .
- the table section 19 is provided with a recess 19 a for accommodating the temperature detecting section 12.
- the concave portion 19 a is provided so as to be located immediately below the reagent portion 28 of the nanosensor 2 when the biosensor 2 is mounted on the mounting portion 10.
- the current value measurement unit 11 is connected to the pair of terminals 17 and is used to measure a response current value when a voltage is applied between the pair of terminals 17. Things.
- the detection unit 12 is for measuring the temperature of the biosensor 2, and is shown in FIG. As clearly shown, it is housed in the recess 19 a of the table section 19. Therefore, when the biosensor 2 is mounted on the mounting section 10, the biosensor 2 is disposed immediately below the reagent section 28 of the biosensor 2.
- the detection unit 12 has a sensor 12A and an acknowledgment unit 12B.
- the sensor 12A is configured as a removable type. i3 ⁇ 4f Unshirube portion 12B, for example Unshiruberitsu is 0. 10cal / (o C-cm- sec) large wood fees than, more preferably, Shaunshiruberitsu is 0. 15cal / (° C-cm- sec ).
- the heat conducting portion 12B covers the temperature sensor 12A in a state of being in contact with the temperature sensor 12A, and is arranged such that its surface 12b is flush with the surface of the table portion 19. Therefore, when the biosensor 2 is mounted on the mounting section 10, the biosensor section 12B can be transferred to the substrate 22 of the biosensor 2, and the temperature of the biosensor 2 can be reduced by the temperature sensor via the heat conducting section 12B. Measured at 12A. Further, since the air-guiding portion 12B is arranged so as to cover the temperature sensor 12A, the surface of the sensor 12A is prevented from being damaged, and foreign matter such as dust is prevented from adhering.
- the calculation unit 13 shown in FIG. 2 is for calculating the concentration of the specific component in the sample based on the measurement result in the current value measurement unit 11.
- the concentration calculation is performed, for example, by applying the measured current value to a curve indicating the relationship between the current value and the concentration.
- Kemama Izumi may be defined as the relationship between ®I value and concentration.
- the concentration calculation is performed by converting the measured current value to a value using a constant fiber I ⁇ , This is done by applying the 3 ⁇ 4 ⁇ value.
- the correction unit 14 corrects the calculation result of the calculation unit 13 in consideration of the information from the temperature detection unit 12.
- the correction unit 14 stores, for example, data relating to a list of correction coefficients. An example of the list is shown in Fig. 6.
- the list is prepared so that the correction coefficient can be calculated from the combination of and the calculated concentration as parameters.
- the final concentration after temperature correction considering the reaction is determined by multiplying the calculation result in the calculation unit 13 by the selected correction coefficient.
- the list is not limited to that shown in FIG. For example, the classification of and concentration can be changed. Are not limited to the values shown in.
- Each of the calculation unit 13 and the correction unit 14 shown in FIG. Although it can be configured with 0M, it is also possible to construct both the calculation unit 13 and the correction unit 14 by connecting multiple memories such as images and ROM to one CPU. ,.
- the display unit 15 shown in FIG. 1 and FIG. 2 is for displaying an error or the like in addition to the calculation result in the correction unit 14, and is composed of, for example, 1CD.
- the power supply 16 shown in FIG. 2 supplies power to each of the units 11 to 15 or applies a voltage between the pair of terminals 17.
- the power supply 16 is composed of a direct current source such as a dry battery or a rechargeable battery.
- each terminal 17 is provided with E between the working electrode 26 and the counter electrode 27 of the biosensor 2 or the amount of electron transfer between the working electrode 26 and the electron mediator. It is used when measuring. For this reason, when the biosensor 2 is mounted on the mounting portion 10, each of the terminals 17 is adapted so that the tip 17 a of the biosensor 2 is transferred to the working electrode 26 of the biosensor 2 and the ends 26 b and 27 b of the counter electrode 27. Are located in Each terminal 17 is configured as a leaf spring obtained by bending a conductor piece. Therefore, when the biosensor 2 is mounted on the mounting portion 10, the tip 17a of the terminal 17 is applied with a pressing force to the working electrode 26 and the ends 26b and 27b of the counter electrode 27. Contact the ends 26b, 27b. As a result, the biosensor 2 is brought into close contact with the table 19 and, consequently, the temperature detector 12. Next, the concentration measurement operation in the analyzer XI will be described.
- the analyzer XI it is first determined whether or not the biosensor 2 is mounted.
- the biosensor 2 When the biosensor 2 is mounted, the working electrode 26 and the counter electrode 27 come into contact with the terminal 17 as well shown in FIG. 5, and the current can be measured in the current value measurement unit 11. Therefore, the determination as to whether or not the force with which the sensor 2 is attached can be made, for example, based on the current value measured by the current value measurement unit 11.
- the determination as to whether or not the biosensor 2 is attached may be made using an optical sensor, a pressure sensor, or the like.
- the biosensor 2 was attached to the analyzer XI. It is determined whether the sample is supplied to 28 or not. Such an operation can be performed based on the current value measured by the current value measuring unit 11. More specifically, the determination can be made based on whether the current value measured by the current value measurement unit 11 has reached a predetermined threshold value or not.
- the reagent section 28 is dissolved by the supply of the sample, and a liquid phase reaction system is constructed in the channel 25. In this liquid-phase reaction system, specific components in the sample are oxidized (or reduced), while the electron mediator is reduced (or oxidized).
- the response current value measured by the current value measurement unit 11 is acquired at that time, and this is used as the basis for the calculation in the calculation unit 13.
- the imprinting force of the ⁇ ⁇ £ between the working electrode 26 and the counter electrode 27 is continued even after the force has been applied.
- the response current value measured by the current value measurement unit 11 when the time has elapsed is used as a basis for the calculation in the calculation unit 13.
- the correction unit 14 determines a correction coefficient based on the information from the detection unit 12 and the calculation result from the calculation unit 13, and multiplies the correction coefficient by the calculation result in the calculation unit 13. Combine to determine final concentration.
- the detection unit 12 is provided in the mounting unit 10 of the analyzer, so that the temperature of the biosensor 2 can be measured. Because of this, In measuring the temperature of the sensor 2, it is not necessary to add a detection function such as a temperature sensor to the pyrosensor 2, and the production cost of the biosensor 2 is low. Further, although the temperature detection unit 12 is provided in the analyzer XI, the temperature detector 12 is configured to measure the temperature of the biosensor 2 instead of the temperature inside the analyzer XI. In particular, if the detection unit 12 is arranged close to the biosensor 2, the force measured by the detection unit 12 becomes closer to that of the S biosensor 2.
- the detection unit 12 is provided so as to be located in the region immediately below the reagent unit 28 or in the vicinity of the reagent unit 28, the measurement measured by the detection unit 12 is closer to the reaction, and the reaction is properly grasped. Will be able to As a result, the concentration calculation can be performed with high accuracy in consideration of the reaction temperature.
- FIGS. 7 to FIG. 9 the same reference numerals are given to the same elements as those in the first embodiment of the present invention described above, and the repeated description will be omitted.
- the analyzer X2 according to the second embodiment differs from the analyzer XI (see FIG. 5 and the like) according to the previous embodiment in the configuration of the detection unit 12 '. .
- the detection unit 12 ′ is stopped and modularized by the sensor 12 A, the heat conduction unit 12 B, and the force S resin package 12 C, and is fitted into the table unit 19 as a module.
- the temperature detecting section is constituted only by the temperature sensor 12A.
- the temperature sensor 12A is arranged such that its surface is exposed at the table section 19. As a result, when the biosensor 2 is mounted on the mounting section 10, the temperature sensor 12A directly penetrates the biosensor 2.
- the analyzer X4 uses a non-lover type sensor as the sensor 12A ".
- the detecting unit 12" further includes a transparent element 12D "
- the surface of the sensor 12A " is prevented from being damaged, and dust on the surface of the sensor 12A” is suppressed. Foreign matter such as adhesion is suppressed.
- the present invention is not limited to the first to fourth embodiments described above, but can be variously designed.
- the detection units 12, 1 and 12 may be arranged at a site (mounting unit) where the measurement of the Noo sensor 2 can be appropriately measured, and need not necessarily be provided in the area immediately below the reagent unit 28.
- the ⁇ 3 ⁇ 43 ⁇ 4 correction unit 14 is not an essential component and can be omitted, for example, in the analyzer, the temperature of the biosensor is displayed on the display unit based on the information from the temperature detection unit.
- a correction table (for example, the one shown in FIG. 6) is preliminarily displayed separately from the analyzer, and the user himself / herself corrects the actually measured value based on the displayed correction table. You can also.
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
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JP2003562626A JP4505837B2 (ja) | 2002-01-18 | 2003-01-14 | 温度検出部を備えた分析装置 |
EP03701080.8A EP1467201B1 (en) | 2002-01-18 | 2003-01-14 | Analyzer having temperature sensor |
US10/501,797 US7655456B2 (en) | 2002-01-18 | 2003-01-14 | Analytical device having temperature detection unit |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2002-9996 | 2002-01-18 | ||
JP2002009996 | 2002-01-18 |
Publications (1)
Publication Number | Publication Date |
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WO2003062812A1 true WO2003062812A1 (en) | 2003-07-31 |
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ID=27605984
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2003/000225 WO2003062812A1 (en) | 2002-01-18 | 2003-01-14 | Analyzer having temperature sensor |
Country Status (5)
Country | Link |
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US (1) | US7655456B2 (ja) |
EP (1) | EP1467201B1 (ja) |
JP (2) | JP4505837B2 (ja) |
CN (1) | CN100344963C (ja) |
WO (1) | WO2003062812A1 (ja) |
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Also Published As
Publication number | Publication date |
---|---|
JP2010091583A (ja) | 2010-04-22 |
CN1618015A (zh) | 2005-05-18 |
JP4505837B2 (ja) | 2010-07-21 |
JP4901964B2 (ja) | 2012-03-21 |
US20050019219A1 (en) | 2005-01-27 |
EP1467201A1 (en) | 2004-10-13 |
CN100344963C (zh) | 2007-10-24 |
EP1467201A4 (en) | 2008-12-24 |
JPWO2003062812A1 (ja) | 2005-05-26 |
US7655456B2 (en) | 2010-02-02 |
EP1467201B1 (en) | 2018-10-31 |
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