WO2011081211A1 - Dispositif de mesure équipé d'un biocapteur - Google Patents

Dispositif de mesure équipé d'un biocapteur Download PDF

Info

Publication number
WO2011081211A1
WO2011081211A1 PCT/JP2010/073829 JP2010073829W WO2011081211A1 WO 2011081211 A1 WO2011081211 A1 WO 2011081211A1 JP 2010073829 W JP2010073829 W JP 2010073829W WO 2011081211 A1 WO2011081211 A1 WO 2011081211A1
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
temperature
biosensor
sample
blood
Prior art date
Application number
PCT/JP2010/073829
Other languages
English (en)
Japanese (ja)
Inventor
滋 関根
勝也 白崎
満洋 森田
Original Assignee
ニプロ株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by ニプロ株式会社 filed Critical ニプロ株式会社
Publication of WO2011081211A1 publication Critical patent/WO2011081211A1/fr

Links

Images

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
    • G01N27/3272—Test elements therefor, i.e. disposable laminated substrates with electrodes, reagent and channels
    • 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
    • C12Q1/001—Enzyme electrodes
    • C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
    • C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose

Definitions

  • the present invention relates to a measuring apparatus in which a biosensor having a first electrode on which an enzyme is immobilized and a second electrode corresponding to the first electrode is detachably provided on the apparatus body.
  • Insulin is known as a drug that controls blood glucose levels and is administered to diabetic patients as a therapeutic agent for diabetes.
  • the need to administer insulin is determined based on the blood glucose level of the diabetic patient. For this reason, it is important for a diabetic patient to grasp a blood glucose level.
  • the blood glucose level is the glucose concentration in the blood.
  • a simple blood glucose measuring device has been developed for the purpose of allowing a diabetic patient to easily measure his blood glucose level.
  • the biosensor has an electrode on which an enzyme that reacts with blood sugar is fixed.
  • Glucose oxidase hereinafter sometimes abbreviated as “GOD”
  • GDH glucose dehydrogenase
  • a biosensor an electrode on which an enzyme is immobilized is called a working electrode, and an electrode that supplies electrons into a sample is called a counter electrode.
  • the working electrode When blood, which is a sample, is introduced into the biosensor and the working electrode GOD reacts with glucose in the blood, glucose is decomposed into gluconic acid and hydrogen peroxide, and the hydrogen peroxide is decomposed into water and electrons. The electrons generated in this way are transmitted to the working electrode. On the other hand, electrons are supplied from the counter electrode into the blood. In this way, a current flows between the working electrode and the counter electrode due to the reaction between GOD and glucose. Then, based on the flowing current value, the glucose concentration in the blood, that is, the blood glucose level is calculated. In addition, a substance that transmits electrons may be fixed to the working electrode. This material is referred to as an electron mediator. Examples of the electron mediator include organic compounds such as potassium ferricyanide, hexaammineruthenium and quinone derivatives, or organic-metal complexes.
  • the electron mediator include organic compounds such as potassium ferricyanide, hexaammineruthenium and quinone derivatives, or
  • the temperature affects the measured value.
  • the temperature characteristics of the resistance for converting the current flowing through the biosensor into voltage, the temperature dependence of the reaction rate of the enzyme, the temperature dependence of the diffusion rate of the mediator, etc. have been pointed out.
  • a configuration is known in which a temperature sensor is provided in a measurement device to which a biosensor is attached and the glucose measurement value is corrected based on the measurement value of the temperature sensor.
  • Patent Documents 5 to 7 Further, a configuration is known in which a part where blood is introduced in a biosensor is brought into contact with a part of a measuring apparatus, and a temperature sensor is used for the part of the contact (Patent Document 8).
  • Patent Document 9 and 10 the structure which provides a heat conductive layer in a biosensor and measures the temperature of the blood introduced into the biosensor through the heat conductive layer is known (patent documents 9 and 10).
  • a configuration is known in which a biosensor is separately provided with an electrode pair that causes a redox reaction for substances other than glucose, and the measured glucose value is corrected based on the current value obtained by the redox reaction. Yes (Patent Document 11).
  • the blood introduction location of the biosensor is arranged so as to overlap a part of the measurement device. There is a need. If it does so, there exists a possibility that the operation
  • the present invention has been made in view of the above-described circumstances, and an object thereof is to provide means capable of accurately and quickly measuring the temperature of a biosensor.
  • the present invention relates to a measuring apparatus having a biosensor that can be attached to and detached from the apparatus main body.
  • the biosensor includes a first electrode on which an enzyme that reacts with a substance to be detected in a sample is fixed, a second electrode electrically corresponding to the first electrode, a third electrode for detecting temperature, It comprises.
  • the apparatus main body includes a quantification means for quantifying the substance to be detected in the sample based on a current flowing between the first electrode and the second electrode as a result of the enzyme reacting with the substance to be detected.
  • the biosensor is for electrochemically detecting a substance to be detected in a biological sample.
  • biological samples include mainly liquids such as blood, saliva, and urine.
  • the substance to be detected include blood glucose, cortisol, cholesterol, neutral fat, hemoglobin, bilirubin, and trace metals such as copper, zinc and iron.
  • the biological sample is brought into contact with the electrode of the biosensor, the biological sample and the enzyme are mixed, and the substance to be detected causes an enzyme reaction.
  • a substance to be detected can be detected electrically by the charge generated in the course of the enzyme reaction flowing to the electrode.
  • the enzyme immobilized on the first electrode is not particularly limited as long as it reacts with the detected substance or the reaction product for electrical detection of the aforementioned detected substance.
  • the detected substance is blood. If it is medium glucose, glucose oxidase or glucose dehydrogenase is mentioned.
  • a mediator may be further fixed to the first electrode.
  • the mediator refers to a substance that transmits electrons generated in the above-described enzymatic reaction process.
  • Examples of mediators used for GOD and GDH include organic compounds such as potassium ferricyanide, hexaammineruthenium and quinone derivatives, or organic-metal complexes.
  • the third electrode is made of a material whose resistance value varies with temperature. If the resistance value and temperature coefficient of the material at the reference temperature are known, the temperature of the third electrode can be calculated from the resistance value measured at the third electrode. In order to accurately calculate the temperature, it is preferable that the temperature coefficient shows a certain large value. Examples of such materials include zinc, aluminum, antimony, gold, silver, copper, and nickel.
  • Biosensor can be attached to the device body.
  • the attachment detection means detects that the biosensor is attached.
  • the pair of connection terminals of the apparatus main body are in electrical contact with the third electrode.
  • a control means operates a temperature calculating means.
  • the temperature calculation means calculates the temperature of the third electrode based on the resistance value between the connection terminals.
  • the correcting means corrects the quantitative value of the substance to be detected determined by the quantitative means based on the temperature of the third electrode.
  • the second electrode may also serve as the third electrode.
  • the biosensor since the biosensor is provided with the third electrode and the temperature is calculated based on the resistance value of the third electrode, the temperature of the biosensor is measured accurately and quickly, and the temperature is measured in the apparatus main body. Based on this, the quantitative value can be corrected.
  • FIG. 1 is a perspective view showing an appearance of a blood glucose measurement device 10 according to an embodiment of the present invention.
  • FIG. 2 is an exploded perspective view of the biosensor 11.
  • FIG. 3 is a block diagram showing an internal configuration of the blood glucose measurement device 10.
  • the blood glucose measurement device 10 includes a biosensor 11 and a device body 12.
  • the biosensor 11 and the apparatus main body 12 are electrically connected by inserting the biosensor 11 into the connection portion 13 of the apparatus main body 12.
  • the biosensor 11 is replaced for each blood glucose measurement.
  • This biosensor 11 corresponds to the biosensor in the present invention.
  • the blood glucose measurement device 10 corresponds to the measurement device according to the present invention.
  • the apparatus main body 12 is an electronic apparatus in which an electronic component is accommodated in a housing 50.
  • a liquid crystal display 51 and operation keys 52, 53, and 54 are disposed on the front side of the housing 50.
  • the operation keys 52, 53, and 54 are for generating corresponding commands based on user operations.
  • the liquid crystal display 51 displays the state of the apparatus main body 12, measurement results, error display, and the like.
  • the liquid crystal display 51 corresponds to display means in the present invention.
  • the internal structure of the apparatus main body 12 will be described later.
  • the biosensor 11 has an elongated sheet shape.
  • the biosensor 11 is attached to the apparatus main body 12 by inserting one end of the biosensor 11 in the longitudinal direction 101 into the connection portion 13 of the apparatus main body 12.
  • the attached biosensor 11 protrudes from the apparatus main body 12 in the longitudinal direction 101. Further, when the biosensor 11 is pulled out in the longitudinal direction 101, the biosensor 11 is removed from the apparatus main body 10.
  • the side inserted into the connecting portion 13 corresponds to the second end in the present invention, and the opposite side corresponds to the first end in the present invention.
  • the front and back of the biosensor 11 are relative, any of them may be front or back.
  • the side that appears in FIG. 1 is referred to as the front, and the side that does not appear in FIG. 1 is referred to as the back. That is, the biosensor 11 has a sheet shape in which the first surface 21 and the second surface 22 are front and back surfaces.
  • the biosensor 11 mainly includes a first substrate 23, a counter electrode 24, a temperature detection electrode 42, a spacer 25, a working electrode 26, a sample detection electrode 27, and a second substrate 28.
  • the first substrate 23, the counter electrode 24 and the temperature detection electrode 42, the spacer 25, the working electrode 26 and the sample detection electrode 27, and the second substrate 28 are stacked in this order, and are elongated in the longitudinal direction 101.
  • a sheet-shaped biosensor 11 is configured.
  • the first substrate 23 is a sheet having substantially the same shape as the biosensor 11 in plan view.
  • the first substrate 23 is made of an electrically insulating material.
  • the electrically insulating material include polyesters such as polyethylene terephthalate (PET) and polymethyl methacrylate (PMMA), fluororesin, polycarbonate, and glass.
  • One surface of the first substrate 23 constitutes the first surface 21.
  • a counter electrode 24 and a temperature detection electrode 42 are provided on the surface 32 opposite to the first surface 21.
  • one end side in the longitudinal direction 101 inserted into the connection portion 13 of the apparatus main body 12 is a narrow portion 29 having a narrow width along the direction 102 orthogonal to the longitudinal direction 101.
  • a pair of colored portions 30 and 31 are formed at both ends in the direction 102.
  • the colored portions 30 and 31 are color-coded with the first surface 21.
  • the coloring portions 30 and 31 are for facilitating visual recognition of the position of a sample introduction port 41 to be described later. Therefore, the coloring portions 30 and 31 are arranged immediately above the sample introduction port 41.
  • the counter electrode 24 is provided on the surface 32 of the first substrate 23 opposite to the first surface 21.
  • the counter electrode 24 occupies about one half of the direction 102 on the surface 32 of the first substrate 23.
  • Examples of the counter electrode 24 include silver / silver chloride, gold, palladium, and platinum.
  • the counter electrode 24 is laminated on the surface 32 with respect to the first substrate 23 by a method such as a screen printing method, an ink jet method, sputtering, vacuum deposition, sol-gel method, cluster beam deposition, or PLD.
  • a portion corresponding to the narrow portion 29 of the first substrate 23 is a connection terminal 33 inserted into the connection portion 13 of the apparatus main body 12.
  • the counter electrode 24 corresponds to the second electrode in the present invention.
  • the temperature detection electrode 42 is provided on the surface 32 of the first substrate 23 opposite to the first surface 21.
  • the temperature detection electrode 42 is disposed so as not to overlap the counter electrode 24 on the surface 32 of the first substrate 23.
  • the temperature detection electrode 42 has a resistance value and a temperature coefficient at a reference temperature unique to the material.
  • the resistance value at the reference temperature is known as a resistance value at 20 ° C., for example.
  • the temperature coefficient is known as a resistance value that changes every time the temperature increases by 1 ° C.
  • Examples of the temperature detection electrode 42 include zinc, aluminum, antimony, gold, silver, copper, and nickel.
  • the temperature detection electrode 42 is laminated on the surface 32 with respect to the first substrate 23 by a method such as a screen printing method, an inkjet method, sputtering, vacuum deposition, sol-gel method, cluster beam deposition, or PLD.
  • the temperature detection electrode 42 corresponds to the third electrode in the present invention.
  • the temperature detection electrode 42 is a U-shape in which two portions that are electrically independently extended from the narrow portion 29 along the longitudinal direction 101 are electrically connected at a portion 45 at a position corresponding to the space 40. It has a shape. In the space 40, a portion including a part 45 of the temperature detection electrode 42 is disposed. The portions corresponding to the narrow portion 29 of the temperature detection electrode 42 are two electrically independent end portions, and these end portions are connection terminals 46 and 47 inserted into the connection portion 13 of the apparatus main body 12. is there.
  • the second substrate 28 is a sheet having substantially the same shape as the biosensor 11 in plan view.
  • the second substrate 28 is made of an electrically insulating material.
  • the electrically insulating material include polyesters such as polyethylene terephthalate (PET) and polymethyl methacrylate (PMMA), fluororesin, polycarbonate, and glass.
  • One surface of the second substrate 28 constitutes the second surface 22.
  • a working electrode 26 and a sample detection electrode 27 are provided on a surface 34 opposite to the second surface 22.
  • a narrow portion 35 having a narrow width along the direction 102.
  • the second surface 22 of the second substrate 28 is formed with colored portions similar to the colored portions 30 and 31.
  • the working electrode 26 is provided on a surface 34 of the second substrate 28 opposite to the second surface 22.
  • the working electrode 26 occupies most of the second substrate 28 other than the periphery of the surface 34, but a recessed portion 36 is formed so that the width in the direction 102 becomes narrow at a position corresponding to a space 40 described later. ing.
  • Examples of the material of the working electrode 26 include carbon. Since carbon is used for the working electrode 26, the resistance value of the first electrode 23 employing silver / silver chloride, gold, palladium, platinum or the like is lower than the resistance value of the working electrode 26 made of carbon. Electrons are easily supplied to 40 blood.
  • the working electrode 26 corresponds to the first electrode in the present invention.
  • connection terminal 37 inserted into the connection portion 13 of the apparatus main body 12. None of the spacer 25, the counter electrode 24, the temperature detection electrode 42, or the first substrate 23 is opposed to the connection terminal 37 and is exposed to the outside of the biosensor 11. Since the working electrode 26 is formed on the surface 34 side of the second substrate 28, the connection terminal 37 is exposed only on the first surface 21 side of the biosensor 11.
  • a GOD and a mediator are fixed to a region 38 corresponding to the space 40.
  • a mediator the compound containing transition metals, such as ruthenium, osmium, molybdenum, tungsten, iron, cobalt, is mentioned, for example.
  • the GOD and the mediator are fixed by applying a liquid containing the GOD and the mediator to the working electrode 26 and drying it.
  • sample detection electrode 27 As shown in FIG. 2, the sample detection electrode 27 is provided on the surface 34 of the second substrate 28 opposite to the second surface 22.
  • the sample detection electrode 27 is elongated in the longitudinal direction 101 on the surface 34 of the second substrate 28 and is bent so that one end thereof enters the recess 36 of the working electrode 26.
  • Examples of the material of the sample detection electrode 27 include silver / silver chloride, gold, palladium, and platinum.
  • the sample detection electrode 27 is an electrode for detecting whether blood is introduced into the space 40.
  • the part corresponding to the narrow part 35 of the second substrate 28 is a connection terminal 39 inserted into the connection part 13 of the apparatus main body 12. None of the spacer 25, the counter electrode 24, the temperature detection electrode 42, or the first substrate 23 is opposed to the connection terminal 39, and is exposed to the outside of the biosensor 11. Since the sample detection electrode 27 is formed on the surface 34 side of the second substrate 28, the connection terminal 39 is exposed only on the first surface 21 side of the biosensor 11.
  • the spacer 25 is a sheet having substantially the same shape as the biosensor 11 in plan view.
  • a double-sided tape having electrical insulation is preferably used.
  • the spacer 25 has a space 40 extending in the direction 102 at a position corresponding to the coloring portions 30 and 31. That is, the spacer 25 is composed of two sheets separated by the space 40 with respect to the longitudinal direction 101.
  • the space 40 forms a sample space corresponding to the thickness of the spacer 25 between the counter electrode 24 and the temperature detection electrode 42 and the working electrode 26 and the sample detection electrode 27. That is, the space 40 becomes the sample space.
  • a part of the counter electrode 24, a part 45 of the temperature detection electrode 42, a part of the working electrode 26, and a part of the sample detection electrode 27 are exposed.
  • the counter electrode 24 and the temperature detection electrode 42, the working electrode 26 and the sample detection electrode 27 are opposed to each other in the space 40 while being separated in the thickness direction of the biosensor 11.
  • the space 40 is opened at the end of the biosensor 11, and this opening serves as the sample introduction port 41.
  • the space 40 is also opened at a position facing the sample introduction port 41.
  • connection portion 13 of the apparatus main body 12 is provided with five connection terminals 61 to 65.
  • the connection terminals 61 to 65 correspond to the connection terminal 33 of the counter electrode 24, the connection terminals 46 and 47 of the temperature detection electrode 42, the connection terminal 37 of the working electrode 26, and the connection terminal 39 of the sample detection electrode 27.
  • the two connection terminals 62 and 63 are electrically connected to the connection terminals 46 and 47 of the temperature detection electrode 42, respectively.
  • the connection terminals 62 and 63 correspond to a pair of connection terminals in the present invention.
  • the apparatus main body 12 is provided with a control unit 70.
  • the control unit 70 is an arithmetic unit configured by a CPU for performing various calculations, a ROM for storing various programs, a RAM for temporarily storing data for various calculations, a bus for transmitting data, and the like.
  • a blood glucose determination unit 71, a sample detection unit 72, a temperature calculation unit 73, a correction unit 74, a liquid crystal display 51, and operation keys 51, 52, and 53 are connected to the control unit 70 so as to be able to transmit and receive electrical signals.
  • the control unit 70 controls each operation of the blood glucose determination unit 71, the sample detection unit 72, the temperature calculation unit 73, the correction unit 74, and the liquid crystal display 51.
  • the control unit 70 corresponds to the control means in the present invention.
  • the blood glucose determination unit 71 calculates a blood glucose level based on the current value flowing between the counter electrode 24 and the working electrode 26 of the biosensor 11, and the current flowing between the counter electrode 24 and the working electrode 26 is calculated. It has a circuit that converts it into a voltage, shapes an electrical signal represented by the voltage, and converts it into a digital signal expressed numerically. Moreover, it has a program which calculates a blood glucose level based on the electric current value which flowed between the counter electrode 24 and the working electrode 26. This program may be stored in the control unit 70. An electrical signal indicating the calculated blood glucose level is stored in the RAM of the control unit 70.
  • the blood sugar quantification unit 71 corresponds to the quantification means in the present invention.
  • the sample detector 72 determines whether a sample has been introduced into the space 40 based on the current value flowing between the counter electrode 24 and the sample detection electrode 27.
  • the control unit 70 requests the blood glucose determination unit 71 to calculate the blood glucose level and the temperature calculation unit 73 to calculate the temperature on the condition that the sample detection unit 72 determines that there is a sample.
  • the temperature calculation unit 73 calculates a temperature based on a resistance value generated between the connection terminals 46 and 47 of the temperature detection electrode 42 and the connection terminals 62 and 63 connected thereto.
  • the temperature calculation unit 73 stores a resistance value and a temperature coefficient at a reference temperature unique to the material of the temperature detection electrode 42, and a resistance value generated between the connection terminals 62 and 63 and a resistance value at the reference temperature are stored.
  • the temperature of the temperature detection electrode 42 is calculated by dividing the difference by the temperature coefficient.
  • An electric signal indicating the calculated temperature is stored in the RAM of the control unit 70.
  • the resistance value and the temperature coefficient at the reference temperature specific to the material of the temperature detection electrode 42 may be stored in the control unit 70.
  • the temperature calculation unit 73 corresponds to the temperature calculation means in the present invention.
  • the correction unit 74 performs temperature correction of the blood glucose level based on each electrical signal indicating the blood glucose level and temperature stored in the RAM of the control unit 70.
  • the correction unit 74 has a table indicating the relationship between the temperature and the correction coefficient.
  • the correction unit 74 selects a correction coefficient corresponding to the temperature stored in the RAM of the control unit 70, and calculates the corrected blood sugar level by multiplying the blood sugar level stored in the RAM by the correction coefficient.
  • An electrical signal indicating the corrected blood glucose level is stored in the RAM of the control unit 70.
  • the correction unit 74 corresponds to the correction unit in the present invention.
  • connection terminals 61 to 65, the connection terminal 33 of the counter electrode 24, the connection terminals 46 and 47 of the temperature detection electrode 42, the connection terminal 37 of the working electrode 26, and the connection terminal 39 of the sample detection electrode 27 are electrically connected. Connected to.
  • the control unit 70 When the biosensor 11 is connected to the apparatus main body 12, a current can flow between the connection terminals 62 and 63 of the apparatus main body 12 via the temperature detection electrode 42.
  • the control unit 70 When the power of the apparatus main body 12 is turned on, the control unit 70 periodically applies a weak potential between the connection terminals 62 and 63, and detects a current flowing between the connection terminals 62 and 63, thereby detecting the biosensor. 11 is attached.
  • the mounting detection means in the present invention is realized.
  • the control unit 70 causes the temperature calculation unit 72 to apply a predetermined potential and current to the temperature detection electrode 42 and measure the resistance value of the temperature detection electrode 42 on the condition that the biosensor 11 has been mounted.
  • the resistance value of the temperature detection electrode 42 is measured as a resistance value with respect to a current flowing from the connection terminal 46 through the part 45 to the connection terminal 47 or a current flowing from the connection terminal 47 through the part 45 to the connection terminal 46.
  • the temperature calculation unit 72 calculates the temperature of the temperature detection electrode 42 based on the resistance value of the temperature detection electrode 42 and the resistance value and temperature coefficient at the reference temperature. An electric signal indicating the calculated temperature is stored in the RAM of the control unit 70.
  • Measured person collects his own blood.
  • the blood can be collected by the person himself / herself using, for example, a lancet. This blood corresponds to the sample in the present invention.
  • the collected blood is introduced into the space 40 from the sample inlet 41 of the biosensor 11 as a sample.
  • the blood is guided to the space 40 by capillary action.
  • a current is generated between the counter electrode 24 and the sample detection electrode 27, and the sample detection unit 72 determines that there is a sample based on this current.
  • the blood introduced into the space 40 is held between the counter electrode 24 and the working electrode 26 and causes an electrochemical reaction.
  • This electrochemical reaction generates a current that correlates with the blood glucose level between the counter electrode 24 and the working electrode 26.
  • the control unit 70 causes the blood glucose determination unit 71 to calculate the blood glucose level based on the current flowing between the counter electrode 24 and the working electrode 26 on the condition that the sample detection unit 72 determines that there is a sample. Note that when blood is introduced into the space 40, the blood contacts the part 45 of the temperature detection electrode 42.
  • the temperature calculation unit 72 measures the resistance value of the temperature detection electrode 42 as soon as the biosensor 11 is attached to the apparatus main body 12, and this measurement ends until the sample detection unit 72 determines that there is a sample. However, the control unit 70 does not apply the potential and current to the connection terminals 62 and 63 on condition that the sample detection unit 72 determines that there is a sample.
  • the control unit 70 causes the correction unit 74 to perform temperature correction of the blood glucose level on the obtained blood glucose level based on the already measured temperature. Then, the controller 70 displays the obtained corrected blood glucose level on the liquid crystal display 51.
  • the temperature detection electrode 42 is provided in the biosensor 11, and the temperature calculation unit 72 calculates the temperature of the temperature detection electrode 42 based on the resistance value of the temperature detection electrode 42. Can be measured accurately and quickly to correct the blood glucose level based on the temperature.
  • the counter electrode 24 and the working electrode 26 are opposed to each other with the space 40 interposed therebetween, and even if an elongated sheet shape is used as a whole, the loss due to heat conduction in the temperature detection electrode 42.
  • the temperature of the biosensor 11 is measured without being affected by the above.
  • the space 40 and the sample introduction port 41 are arranged on the side opposite to the side connected to the connection portion 13 of the apparatus main body 12, blood is introduced at the distal end side of the biosensor 11 protruding from the apparatus main body 12. This facilitates introduction of blood into the space 40 and facilitates the attachment of blood to the apparatus main body 12.
  • the enzyme contained in the reagent is GOD, but it goes without saying that the enzyme in the present invention is not limited to GOD.
  • GDH may be included in the reagent as an enzyme instead of GOD.
  • the configuration of the biosensor 11 shown in the present embodiment is only one aspect of the configuration of the biosensor according to the present invention. Therefore, instead of the three-dimensional type in which the counter electrode 24 and the working electrode 26 are opposed to each other via the spacer 25 like the biosensor 11, the bio-type is a planar type in which the working electrode and the counter electrode are arranged on the same substrate. A sensor may be realized.
  • the biosensor according to the present invention is not limited to the portable blood glucose measurement device like the blood glucose measurement device 10. Therefore, when a biosensor is used for measuring other components in blood, it can also be used in an embodiment in which a reagent containing an enzyme necessary for the measurement is fixed to the electrode.
  • the sample is not limited to blood, and may be a biological sample such as urine or saliva, or an aqueous solution containing a substance to be detected.
  • the temperature detection electrode 42 is provided independently of the working electrode 24, the counter electrode 26, and the sample detection electrode 27 in the biosensor 11, but the temperature detection electrode 42 is provided as the counter electrode 26 or the sample detection electrode 27. May also be served.
  • two connection terminals are connected to the connection terminal 37 of the counter electrode 26 that also serves as the temperature detection electrode 42 or the connection terminal 39 of the sample detection electrode 27 in the connection part 13 of the apparatus body 12. Since no enzyme or mediator is fixed to the counter electrode 26 or the sample detection electrode 27, even if a potential or current is applied through the two connection terminals of the connection unit 13 before blood is introduced into the biosensor 11, There is no electrical effect on the enzyme or mediator. Thereby, size reduction and cost reduction of the biosensor 11 and the apparatus main body 12 are implement
  • a mode is shown in which the control unit 70 detects that the biosensor 11 is attached to the apparatus main body 12 based on a change in current between the connection terminals 62 and 63.
  • the control unit 70 detects that the biosensor 11 is attached to the apparatus main body 12 based on a change in current between the connection terminals 62 and 63.
  • a configuration may be adopted in which the biosensor 11 is mechanically detected by providing the connection portion 13 with a mechanical switch that can be pressed by the biosensor 11.
  • a configuration in which the biosensor 11 is optically detected by providing a photo interrupter that is shielded by the sensor 11 may be employed.

Landscapes

  • Chemical & Material Sciences (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Organic Chemistry (AREA)
  • Molecular Biology (AREA)
  • Zoology (AREA)
  • Biophysics (AREA)
  • Proteomics, Peptides & Aminoacids (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Immunology (AREA)
  • Biochemistry (AREA)
  • Physics & Mathematics (AREA)
  • Analytical Chemistry (AREA)
  • Wood Science & Technology (AREA)
  • Emergency Medicine (AREA)
  • Microbiology (AREA)
  • Bioinformatics & Cheminformatics (AREA)
  • General Engineering & Computer Science (AREA)
  • Biotechnology (AREA)
  • Genetics & Genomics (AREA)
  • Hematology (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Electrochemistry (AREA)
  • General Physics & Mathematics (AREA)
  • Pathology (AREA)
  • Investigating Or Analysing Biological Materials (AREA)

Abstract

L'invention concerne un dispositif de mesure équipé d'un biocapteur pouvant être enlevé d'un dispositif principal. Le biocapteur comporte: une première électrode; une deuxième électrode; et une troisième électrode pour mesurer une température. Le dispositif principal comporte: des moyens de mesure d'une quantité qui mesurent la quantité d'une matière voulue dans un échantillon, sur la base du courant s'écoulant entre la première électrode et la deuxième électrode et qui résulte de la réaction de l'oxygène avec la matière voulue; deux bornes de connexion qui se connectent électriquement à la troisième électrode; des moyens de calcul de température qui calculent la température de la troisième électrode sur la base de la résistance de la troisième électrode, obtenue entre les bornes de connexion; des moyens de correction qui corrigent, sur la base de la température calculée par les moyens de calcul de température, la quantité de matière voulue mesurée par les moyens de mesure de quantité; des moyens de détection de fixation qui détectent que le biocapteur est fixé; et des moyens de commande qui font en sorte que les moyens de calcul de température calculent la température de la troisième électrode si les moyens de détection de fixation ont détecté que le biocapteur était fixé.
PCT/JP2010/073829 2009-12-29 2010-12-29 Dispositif de mesure équipé d'un biocapteur WO2011081211A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2009-299075 2009-12-29
JP2009299075A JP2011137769A (ja) 2009-12-29 2009-12-29 バイオセンサを有する測定装置

Publications (1)

Publication Number Publication Date
WO2011081211A1 true WO2011081211A1 (fr) 2011-07-07

Family

ID=44226613

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2010/073829 WO2011081211A1 (fr) 2009-12-29 2010-12-29 Dispositif de mesure équipé d'un biocapteur

Country Status (2)

Country Link
JP (1) JP2011137769A (fr)
WO (1) WO2011081211A1 (fr)

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN102841118A (zh) * 2012-08-16 2012-12-26 江苏学府医疗科技有限公司 一种使用温度传感器调控的便携式智能血糖仪
WO2013070779A3 (fr) * 2011-11-09 2013-11-28 Telcare, Inc. Glucomètre portatif ayant une capacité de messagerie
CN105143870A (zh) * 2013-04-26 2015-12-09 松下健康医疗控股株式会社 液体试样测定装置、液体试样测定方法以及生物传感器
CN105873533A (zh) * 2014-03-26 2016-08-17 奥林匹斯冬季和Ibe有限公司 泌尿科器械

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9823214B2 (en) 2011-11-01 2017-11-21 Panasonic Healthcare Holdings Co., Ltd. Biological sample measuring apparatus
KR20190063762A (ko) * 2017-11-30 2019-06-10 비케이전자 주식회사 온도 센서를 구비한 뇨당 검출 장치

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002257782A (ja) * 2001-03-05 2002-09-11 Nec Corp 電気化学センサ測定装置
JP2005265629A (ja) * 2004-03-18 2005-09-29 Nokodai Tlo Kk カード型標的物質検出装置
JP2006516720A (ja) * 2003-02-01 2006-07-06 エフ．ホフマン−ラ　ロシュ　アーゲー サーモスタット制御なしに凝固時間を計測するためのシステムおよび方法
WO2007102347A1 (fr) * 2006-02-27 2007-09-13 Sumitomo Electric Industries, Ltd. Puce de biocapteur, systeme de biocapteur et leur dispositif de mesure

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002257782A (ja) * 2001-03-05 2002-09-11 Nec Corp 電気化学センサ測定装置
JP2006516720A (ja) * 2003-02-01 2006-07-06 エフ．ホフマン−ラ　ロシュ　アーゲー サーモスタット制御なしに凝固時間を計測するためのシステムおよび方法
JP2005265629A (ja) * 2004-03-18 2005-09-29 Nokodai Tlo Kk カード型標的物質検出装置
WO2007102347A1 (fr) * 2006-02-27 2007-09-13 Sumitomo Electric Industries, Ltd. Puce de biocapteur, systeme de biocapteur et leur dispositif de mesure

Cited By (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2013070779A3 (fr) * 2011-11-09 2013-11-28 Telcare, Inc. Glucomètre portatif ayant une capacité de messagerie
US9064034B2 (en) 2011-11-09 2015-06-23 Telcare, Inc. Handheld blood glucose monitoring device with messaging capability
US9739744B2 (en) 2011-11-09 2017-08-22 Telcare, Llc Handheld blood glucose monitoring device with messaging capability
CN102841118A (zh) * 2012-08-16 2012-12-26 江苏学府医疗科技有限公司 一种使用温度传感器调控的便携式智能血糖仪
CN105143870A (zh) * 2013-04-26 2015-12-09 松下健康医疗控股株式会社 液体试样测定装置、液体试样测定方法以及生物传感器
CN105143870B (zh) * 2013-04-26 2018-03-20 松下健康医疗控股株式会社 液体试样测定装置、液体试样测定方法以及生物传感器
US10317360B2 (en) 2013-04-26 2019-06-11 Phc Holdings Corporation Liquid sample measurement device, liquid sample measurement method, and biosensor
US11268926B2 (en) 2013-04-26 2022-03-08 Phc Holdings Corporation Liquid sample measurement device, liquid sample measurement method, and biosensor
CN105873533A (zh) * 2014-03-26 2016-08-17 奥林匹斯冬季和Ibe有限公司 泌尿科器械

Also Published As

Publication number Publication date
JP2011137769A (ja) 2011-07-14

Similar Documents

Publication Publication Date Title
JP4964552B2 (ja) 迅速な電気化学的分析のための方法および装置
JP4505837B2 (ja) 温度検出部を備えた分析装置
CA2794978C (fr) Methode et systeme de mesure d'analyte
JP5982022B2 (ja) 試験片、測定装置、及び測定方法
CA2724911C (fr) Procede et systeme de mesure du plein
KR101966611B1 (ko) 오류 검출을 갖는 포도당 전기화학 측정 방법
WO2011081211A1 (fr) Dispositif de mesure équipé d'un biocapteur
JP5973444B2 (ja) ヘマトクリット補正を有する分析物測定方法及びシステム
JP2013257319A5 (fr)
US9709521B2 (en) System and method for measuring an analyte in a sample and correcting for interferents
CA2806064A1 (fr) Systeme et procede de mesure d'un analyte dans un echantillon
RU2670215C1 (ru) Точные измерения аналита с помощью электрохимической тест-полоски для определения времени измерения аналита на основании измеренной температуры, физической характеристики и оценочной концентрации аналита и их температурно-компенсированных величин
JP5509969B2 (ja) 測定装置及び測定方法
JP2011137767A (ja) バイオセンサ、及び当該バイオセンサを有する測定装置
WO2018141799A1 (fr) Détermination d'une concentration en analyte d'un fluide physiologique ayant un interférent
JP5115535B2 (ja) 生体試料検出装置
EP2956765B9 (fr) Système et procédé pour mesurer un analyte dans un échantillon et calculer des concentrations de glucose indépendamment des hématocrites
WO2017021534A1 (fr) Système et procédé pour compenser des mesures d'échantillon à l'aide de bandes de test
JP5251859B2 (ja) バイオセンサ
CA2934809A1 (fr) Circuit de commande a courant constant d'appareil d'analyse portatif comportant une detection integree de bandelette reactive
JP2014102144A (ja) 糖化ヘモグロビン測定キットおよび糖化ヘモグロビン測定方法
AU2022400944A1 (en) Systems and methods for hematocrit impedance measurement using 4-wire measurement
AU2014262270A1 (en) Electrochemical analyte measurement method and system

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 10841066

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 10841066

Country of ref document: EP

Kind code of ref document: A1