JP2011133294A - Biosensor - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a means for rapidly filling a sample space with a sample in a biosensor wherein first and second electrodes are arranged in counter relationship through a sample space. <P>SOLUTION: One of regions 38 and 42 is coated with one component selected from a group consisting of a water-soluble polymer, a hemolytic agent and a surfactant among the respective components of a reagent containing enzyme, a mediator, the water-soluble polymer, the hemolytic agent, the surfactant and a buffer solution and the other components are applied to the other one of the regions 38 and 42. By this constitution, a space 40 is rapidly filled with the sample. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a biosensor in which each component of a reagent including an enzyme, a mediator, a water-soluble polymer, a hemolytic agent, a surfactant, and a buffer solution is applied to a first electrode or a second electrode.

  In recent years, the number of diabetic patients is increasing in each country. As a treatment for diabetes, for example, there is insulin therapy. 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.

  As the blood glucose measurement device described above, one using a biosensor is known (Patent Documents 1 to 4). The biosensor has an electrode on which an enzyme that reacts with blood sugar is fixed. Glucose oxidase (hereinafter sometimes abbreviated as “GOD”) and glucose dehydrogenase (hereinafter sometimes abbreviated as “GDH”) are known as enzymes used for blood glucose level measurement. . In 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.

  When blood as a sample is introduced into the biosensor and GOD of the working electrode 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.

  In the biosensor described above, an enzyme such as GOD or GDH is fixed by making it into an aqueous solution and applying it to the electrode. Specifically, a dipping method, a screen printing method, an offset printing method, an ink jet printing method, and the like are known (Patent Documents 6 to 8).

  Moreover, in the biosensor described above, it is known that a cationic surfactant (fatty acid) is contained in an aqueous solution of an enzyme or the like applied to an electrode (Patent Document 9). By containing a cationic surfactant, red blood cells (hematocrit value) in a blood sample are hemolyzed, and even in a blood sample with a relatively high viscosity, the blood sugar level can be quickly increased with less error. There is an advantage that it is measured.

JP 2009-97877 A JP 2005-43280 A JP-A-2005-37335 JP 2002-107325 A JP 9-159642 A JP 2006-125904 A Special table 2009-553374 gazette JP-A-6-3317 Japanese Patent No. 4018082

  In the biosensor described above, a configuration in which a space formed by a spacer is a sample space is known. The sample space is opened outside the biosensor. When the opening is exposed to blood, blood is guided to the sample space by capillary action. Therefore, the time from when the opening is exposed to blood until the sample space is filled with blood depends on capillary action. This time is desirably as early as possible from the viewpoint of realizing quick measurement.

  The present invention has been made in view of the above-described circumstances, and an object of the present invention is to quickly move a sample to a sample space in a biosensor in which a sample space is formed by a first surface and a second surface arranged to face each other. It is to provide means to be satisfied.

The present invention is a biosensor including a first electrode, a second electrode, a sample space into which a specimen is introduced, and a reagent. The sample space is formed between a first surface including at least a part of the first electrode and a second surface disposed to face the first surface. The reagent includes an enzyme, a mediator, a water-soluble polymer, a hemolytic agent, a surfactant, and a buffer solution. Each component of the reagent is applied in the following mode (A) or (B).
(A) Among the components of the reagent, any one component selected from the group consisting of a water-soluble polymer, a hemolytic agent, and a surfactant is applied to one of the first surface and the second surface, and the other Is applied to the other of the first surface and the second surface.
(B) Among the components of the reagent, a water-soluble polymer, a hemolytic agent, and a surfactant are applied to the first surface and the second surface.

  The biosensor is for electrochemically detecting a substance to be detected in a specimen. Examples of the specimen include mainly liquids such as blood, saliva, and urine. For example, if the sample is blood, examples of the substance to be detected include blood glucose, cortisol, cholesterol, neutral fat, hemoglobin, bilirubin, and trace metals such as copper, zinc, and iron. When the specimen is brought into contact with the electrode of the biosensor, the specimen 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 contained in the reagent is not particularly limited as long as it reacts with the test substance or the reaction product for the electrical detection of the target substance described above. For example, the target substance is glucose in blood. If so, glucose is decomposed to generate electrons. Specific examples of the enzyme include glucose oxidase, glucose dehydrogenase, glucose dehydrogenase using flavin adenine dinucleotide as a coenzyme, and glucose dehydrogenase using pyrroloquinoline quinone as a coenzyme.

  The mediator contained in the reagent, for example, transmits electrons generated by the decomposition of glucose by the enzyme described above to the first electrode or the second electrode. Specifically, as the mediator, potassium ferricyanide, potassium ferrocyanide, etc. Dimethylferrocene, ferricinium, hexaammineruthenium compound, osmium compound, hydroquinone and the like.

  The water-soluble polymer contained in the reagent forms a film on the first surface or the second surface. Thereby, the other components contained in the reagent are easily fixed to the first surface or the second surface, and the enzyme activity is stabilized. Specific examples of the water-soluble polymer include polyvinyl pyrrolidone, carboxymethyl cellulose, hydroxymethyl cellulose, hydroxyethyl cellulose, hydroxypropyl cellulose, polyvinyl alcohol, polyfluorosulfonate, cellulose acetate, and dextran.

  The hemolytic agent contained in the reagent is used to hemolyze blood as a specimen. Thereby, the measurement of the test substance by the enzyme reaction is rapidly performed without depending on the viscosity of the blood as the specimen. Specific examples of the hemolytic agent include ammonium chloride, sodium cholate, sodium deoxycholate, tetradecyltrimethylammonium bromide, dodecyltrimethylammonium bromide, cetyltrimethylammonium bromide, octadecyltrimethylammonium bromide and the like.

  The surfactant contained in the reagent is for smoothly mixing each component of the reagent. Specifically, Triton (trademark), Tween (trademark), Brij (trademark), etc. are mentioned as surfactant.

  The buffer contained in the reagent adjusts the pH of the reagent in order to obtain stable measurement conditions. Specifically, examples of the buffer include MES buffer, PBS buffer, TRIS buffer, PIPES buffer, MOPS buffer, HEPES buffer, and CAPS buffer.

  According to the present invention, among the components of the reagent including an enzyme, a mediator, a water-soluble polymer, a hemolyzing agent, a surfactant, and a buffer solution, selected from the group consisting of a water-soluble polymer, a hemolytic agent, and a surfactant Either one of the components is applied to one of the first surface or the second surface and the other component is applied to the other of the first surface or the second surface, or among the components of the reagent, Since the water-soluble polymer, hemolytic agent and surfactant are applied to the first surface and the second surface, the sample is quickly filled into the sample space. Thereby, rapid measurement of the test substance is realized.

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.

  Hereinafter, preferred embodiments of the present invention will be described with reference to the drawings as appropriate. Each embodiment described below is only an example of the present invention, and it is needless to say that the embodiment of the present invention can be changed as appropriate without departing from the gist of the present invention.

[Blood glucose measuring device 10]
As shown in FIG. 1, 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.

[Apparatus body 12]
As shown in FIG. 1, 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.

[Biosensor 11]
As shown in FIG. 1, 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. Further, when the biosensor 11 is pulled out in the longitudinal direction 101, the biosensor 11 is removed from the apparatus main body 10.

  Since the front and back of the biosensor 11 are relative, any of them may be front or back. In this embodiment, 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 front surface 21 and the back surface 22 form front and back surfaces.

  As shown in FIG. 2, the biosensor 11 mainly includes a first substrate 23, a first electrode 24, a spacer 25, a second electrode 26, a third electrode 27, and a second substrate 28. 2, the first substrate 23, the spacer 25, the first electrode 24, the second electrode 26, the third electrode 27, and the second substrate 28 are sequentially stacked in this order, and the sheet-shaped biosensor 11 is formed. It is configured.

[First substrate 23]
As shown in FIG. 2, the first substrate 23 is a sheet that is substantially the same shape as the biosensor 11 in plan view and is slightly shorter than the second substrate 24 in the longitudinal direction 101. The first substrate 23 is made of an electrically insulating material. Examples of 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 surface 21. On the surface 21 of the first substrate 23, 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 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.

  As will be described later, each component of the reagent is fixed to a region 42 corresponding to the space 40 in the first substrate 23. Details of each component of the reagent will be described later. Of the surface facing the spacer 25 side in the first substrate 23, the region 42 to which the reagent is applied corresponds to the second surface in the present invention.

[Second substrate 28]
As shown in FIG. 2, 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. Examples of 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 back surface 22. As will be described later, a first electrode 24, a second electrode 26, and a third electrode 27 are provided on the surface 34 opposite to the back surface 22. In the second substrate 28, one end side in the longitudinal direction 101 inserted into the connection portion 13 of the apparatus main body 12 is not opposed to the first substrate 23.

  Although not appearing in each figure, a colored portion similar to the colored portions 30 and 31 is formed on the back surface 22 of the second substrate 28.

[First electrode 24]
As shown in FIG. 2, the first electrode 24 is provided on the surface 34 of the second substrate 28 opposite to the back surface 22. The first electrode 24 extends in the longitudinal direction 101 on the surface 34 of the second substrate 28, and has a width of about 1/3 of the second substrate 28 in the direction 102. On the surface 24, the first electrode 24 is disposed in an electrically unconnected manner with a second electrode 26 and a third electrode 27 described later. Examples of the material for the first electrode 24 include silver / silver chloride, gold, palladium, and platinum. The first electrode 24 is laminated on the surface 34 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. In the first electrode 24, the end corresponding to the connection portion 13 side of the apparatus main body 12 is exposed without facing the first substrate 23. This end is a connection terminal 33 that is electrically connected to the apparatus main body 12.

[Second electrode 26]
As shown in FIG. 2, the second electrode 26 is provided on the surface 34 opposite to the back surface 22 of the second substrate 28. The second electrode 26 extends in the longitudinal direction 101 on the surface 34 of the second substrate 28, and has a width of about 1/3 of the second substrate 28 in the direction 102. On the surface 24, the second electrode 26 is disposed in an electrically unconnected manner with the first electrode 24 and a third electrode 27 described later. An example of the material of the second electrode 26 is carbon. Since carbon is used for the second 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 second electrode 26 made of carbon. Electrons are easily supplied to the blood in the space 40. Of course, the second electrode 26 may be made of a material such as silver / silver chloride, gold, palladium, platinum or the like, like the first electrode 24. In the second electrode 26, an end corresponding to the connection portion 13 side of the apparatus main body 12 is exposed without facing the first substrate 23. This end is a connection terminal 37 that is electrically connected to the apparatus main body 12.

[Third electrode 27]
As shown in FIG. 2, the third electrode 27 is provided on the surface 34 of the second substrate 28 opposite to the back surface 22. The third electrode 27 extends in the longitudinal direction 101 on the surface 34 of the second substrate 28, and has a width of about 1/3 of the second substrate 28 in the direction 102. On the surface 24, the third electrode 27 is disposed in an electrically unconnected manner with the first electrode 24 and the second electrode 26. Examples of the material of the third electrode 27 include silver / silver chloride, gold, palladium, platinum, and the like. The third electrode 27 is an electrode for detecting whether blood is introduced into the space 40. In the third electrode 27, the end corresponding to the connection portion 13 side of the apparatus main body 12 is exposed without facing the first substrate 23. This end is a connection terminal 39 that is electrically connected to the apparatus main body 12.

[Spacer 25]
As shown in FIG. 2, the spacer 25 is a sheet having substantially the same shape as the biosensor 11 in plan view. As the spacer 25, 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 region 38 and the region 42. That is, the space 40 becomes the sample space. In the space 40, a part of the first electrode 24, a part of the second electrode 26, and a part of the third electrode 27 are exposed.

  In the first electrode 24, each component of the reagent is fixed in a region 38 corresponding to the space 40. Details of each component of the reagent will be described later. In the first electrode 24, the region 38 to which the reagent is applied out of the surface facing the spacer 25 corresponds to the first surface in the present invention.

  As shown in FIG. 1, the space 40 is opened at the end of the biosensor 11, and this opening serves as the sample introduction port 41. Although not shown in FIG. 1, the space 40 is also opened at a position facing the sample introduction port 41. When the sample inlet 41 is exposed to blood, blood flows into the space 40 by capillary action.

[Components of Reagent Fixed to Regions 38 and 42]
Hereinafter, the components of the reagent fixed to the regions 38 and 42 will be described in detail. This reagent includes glucose oxidase, mediator, water-soluble polymer, hemolytic agent, surfactant and buffer. The reagent may further contain other components.

  The reagent is prepared by dividing it into a first reagent applied to the region 38 and a second reagent applied to the region 42. The first reagent includes any one component of a water-soluble polymer, a hemolytic agent, and a surfactant that are components of the reagent. The second reagent includes the remaining components of the water-soluble polymer, hemolytic agent, and surfactant that are components of the reagent.

Therefore, in the first reagent and the second reagent, the combinations of the composition of the water-soluble polymer, hemolyzing agent, and surfactant that are the components of the reagent are the following six patterns.
(1) First reagent: surfactant Second reagent: water-soluble polymer, hemolytic agent (2) First reagent: hemolytic agent Second reagent: water-soluble polymer, surfactant (3) First reagent: water-soluble Second Polymer: Hemolytic Agent, Hemolytic Agent (4) First Reagent: Hemolytic Agent, Surfactant Second Reagent: Water-soluble Polymer (5) First Reagent: Water-soluble Polymer, Surfactant Second Reagent: hemolytic agent (6) 1st reagent: water-soluble polymer, hemolytic agent 2nd reagent: surfactant

  Note that glucose oxidase, mediator, and buffer may be included in either the first reagent or the second reagent, but as in the present embodiment, the first electrode 24 functions as a working electrode, and the region 38 If one reagent is applied, the enzyme and mediator are preferably included in the first reagent. Moreover, a well-known method is employ | adopted as the method of apply | coating a 1st reagent and a 2nd reagent to the area | regions 38 and 42, respectively. Examples of such known methods include a dipping method, a screen printing method, an offset printing method, and an ink jet printing method.

[Operational effects of this embodiment]
According to the present embodiment, among the components of the reagent including an enzyme, a mediator, a water-soluble polymer, a hemolyzing agent, a surfactant, and a buffer, it is selected from the group consisting of a water-soluble polymer, a hemolytic agent, and a surfactant. Since one of the components is applied to one of the regions 38 and 42 and the other component is applied to the other of the regions 38 and 42, the blood is quickly filled into the space 40 from the sample introduction port 41. As a result, in the biosensor 11, the glucose oxidase fixed to the region 38 of the first electrode 24 and the glucose in the blood react quickly, and a rapid blood sugar level measurement is realized.

  In the present embodiment, the enzyme contained in the reagent is glucose oxidase, but it goes without saying that the enzyme contained in the reagent of the present invention is not limited to glucose oxidase. For example, in the case of a biosensor used for blood glucose measurement, glucose dehydrogenase may be included in the reagent as an enzyme instead of glucose oxidase.

  Further, 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 sample such as urine or saliva, or may be an aqueous solution containing a substance to be detected.

[Modification]
In the embodiment described above, the first reagent includes any one component of a water-soluble polymer, a hemolytic agent, and a surfactant that are components of the reagent, and the second reagent is a water-soluble component that is a component of the reagent. The remaining components of the soluble polymer, hemolytic agent, and surfactant are included, but both the first reagent and the second reagent include the water-soluble polymer, hemolytic agent, and surfactant that are components of the reagent. May be. Also in the modified example, the glucose oxidase, the mediator, and the buffer may be included in either the first reagent or the second reagent. However, as in the present embodiment, the first electrode 24 functions as a working electrode, If the first reagent is applied to the region 38 of the one electrode 24, the enzyme and the mediator are preferably included in the first reagent.

Therefore, in the modified example, the composition of the first reagent and the second reagent is as follows.
First reagent: glucose oxidase, mediator, water-soluble polymer, hemolytic agent, surfactant Second reagent: water-soluble polymer, hemolytic agent, surfactant, buffer

  Also in such a modification, as in the above-described embodiment, blood is rapidly filled from the sample introduction port 41 into the space 40, and the glucose oxidase fixed to the region 38 of the first electrode 24 in the biosensor 11. And glucose in blood reacts quickly, and rapid blood glucose level measurement is realized.

  Examples of the present invention will be described below.

[Biosensor]
As the biosensor, the biosensor 11 having the same configuration as that of the above-described embodiment was used. Carbon was used as a material for the first electrode 24, the second electrode 26 and the third electrode 27. The reagent was applied to the regions 38 and 42 by using a dispenser according to Examples 1 to 7, Comparative Examples 1 and 2, and Table 1 described later.

[Example 1]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: enzyme (glucose dehydrogenase with flavin adenine dinucleotide as a coenzyme
Nase: FAD-GDH)
Mediator (potassium ferricyanide)
Water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Buffer solution (MES buffer solution)
Second reagent: surfactant (trade name: Triton X-100)

[Example 2]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Water-soluble polymer (polyvinylpyrrolidone; PVP)
Surfactant (trade name: Triton X-100)
Buffer solution (MES buffer solution)
Second reagent: hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)

[Example 3]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)
Buffer solution (MES buffer solution)
Second reagent: water-soluble polymer (polyvinylpyrrolidone; PVP)

[Example 4]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Water-soluble polymer (polyvinylpyrrolidone; PVP)
Buffer solution (MES buffer solution)
Second reagent: hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)

[Example 5]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Buffer solution (MES buffer solution)
Second reagent: water-soluble polymer (polyvinylpyrrolidone; PVP)
Surfactant (trade name: Triton X-100)

[Example 6]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Surfactant (trade name: Triton X-100)
Buffer solution (MES buffer solution)
Second reagent: water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)

[Example 7]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)
Buffer solution (MES buffer solution)
Second reagent: water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)

[Comparative Example 1]
The following 2nd reagent was apply | coated to the area | region 38 of the biosensor by the composition and application quantity which were shown in Table 1, and nothing was apply | coated to the area | region 42. FIG.
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)
Buffer solution (MES buffer solution)
Second reagent: None

[Comparative Example 2]
The composition of the first reagent applied to the area 38 of the biosensor 11 and the composition of the second reagent applied to the area 42 were as follows, and the compositions and application amounts shown in Table 1 were applied to the areas 38 and 42, respectively. .
First reagent: Enzyme (FAD-GDH)
Mediator (potassium ferricyanide)
Buffer solution (MES buffer solution)
Second reagent: water-soluble polymer (polyvinylpyrrolidone; PVP)
Hemolytic agent (tetradecyltrimethylammonium bromide; MTAB)
Surfactant (trade name: Triton X-100)

[Evaluation test]
The evaluation test was performed by measuring the suction time with a potentiostat. A blood sample is sucked from the sample introduction port 41 on the first electrode 24 side of the space 40, and the time when the current is generated between the first electrode 24 and the second electrode 26 is set as a start time. The time when the current was generated between the electrode 27 and the electrode 27 was defined as the end time. The time required from the start time to the end time was taken as the suction time. The results are shown in Table 1.

  As shown in Table 1, in each of Examples 1 to 7, the average value was less than 1.02, whereas Comparative Examples 1 and 2 were significantly slower than the latest Example 7. Accordingly, it was confirmed that the introduction speed of blood into the space 40 by capillary action was increased by each of Examples 1 to 7.

11 ... biosensor 24 ... first electrode 26 ... second electrode 40 ... space (sample space)

Claims (3)

A first electrode, a second electrode, a sample space into which a specimen is introduced, and a reagent,
The sample space is formed between a first surface including at least a part of the first electrode and a second surface disposed to face the first surface,
The reagent includes an enzyme, a mediator, a water-soluble polymer, a hemolytic agent, a surfactant and a buffer solution,
A biosensor in which each component of the reagent is applied in the following mode (A) or (B).
(A) Among the components of the reagent, any one component selected from the group consisting of a water-soluble polymer, a hemolytic agent, and a surfactant is applied to one of the first surface and the second surface, and the other Is applied to the other of the first surface and the second surface.
(B) Among the components of the reagent, a water-soluble polymer, a hemolytic agent, and a surfactant are applied to the first surface and the second surface. A first electrode, a second electrode, a sample space into which a specimen is introduced, and a reagent,
The sample space is formed between a first surface including at least a part of the first electrode and a second surface disposed to face the first surface,
The reagent includes an enzyme, a mediator, a water-soluble polymer, a hemolytic agent, a surfactant and a buffer solution,
Among the components of the reagent, any one component selected from the group consisting of a water-soluble polymer, a hemolytic agent, and a surfactant is applied to one of the first surface and the second surface, and the other component is A biosensor applied to the other of the first surface or the second surface. A first electrode, a second electrode, a sample space into which a specimen is introduced, and a reagent,
The sample space is formed between a first surface including at least a part of the first electrode and a second surface disposed to face the first surface,
The reagent includes an enzyme, a mediator, a water-soluble polymer, a hemolytic agent, a surfactant and a buffer solution,
A biosensor in which a water-soluble polymer, a hemolytic agent, and a surfactant are applied to the first surface and the second surface among the components of the reagent.

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