JP2004004017A - Biosensor and manufacturing method of the biosensor - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a biosensor in which can precisely and exactly measure, and to provide a manufacturing method of a biosensor in which liquid sample can surely be sucked inside a capillary. <P>SOLUTION: The biosensor includes an electrode system, consisting of at least measuring extreme and counter electrode prepared on an insulating substrate, spacers overlapped so that the part of the electrode system is made to face, and space is formed, a reactive reagent section in which the electrode system of area within space is formed on including insulating substrate, a cover plate overlapped by the spacers, and a capillary whose space surrounded by the insulating substrate, spacers and cover plate as a liquid sample passage. In the biosensor, a hydrophilic resin layer is formed over the entire face, in which the electrode system of the insulating substrate is formed, electroless plating plies or layers consisting of the electrode system is formed on this hydrophilic resin layer, and the hydrophilic resin layer is exposed to surroundings of pattern of the electrode system. <P>COPYRIGHT: (C)2004,JPO

Description

[0001]
TECHNICAL FIELD OF THE INVENTION
The present invention relates to a biosensor and a biosensor manufacturing method capable of accurately and accurately measuring a specific component in a small amount of a liquid sample in fields such as food analysis, medical analysis, and environmental analysis. .
[0002]
[Prior art]
Conventionally, there is a biosensor as shown in an exploded perspective view of FIG. This is because a conductive paste is printed by screen printing on an insulating substrate 1 such as a polyethylene terephthalate sheet or the like, and a measurement electrode 4 having terminals 2 and 3 having a substantially convex shape in plan view and a counter electrode having a substantially concave shape in plan view. 5 is formed in a film shape. Further, an insulating layer 6 is printed leaving a strip-shaped region where the junctions of the measuring electrode 4 and the counter electrode 5 are arranged in the vertical direction and regions of the terminal portions 2 and 3 of the measuring electrode 4 and the counter electrode 5. A spacer 7 is disposed so as to overlap with the above, and a reaction reagent composition 9 is formed on the measurement electrode 4 and the counter electrode 5 of the strip-shaped space 8 formed by the spacer 7 by applying a reaction reagent composition or the like. are doing. Then, by covering with a cover plate 10 having a through hole 11, a space 8 surrounded by the insulating substrate 1, the spacer 7 and the cover plate 10 forms a capillary as a liquid sample passage.
[0003]
At the time of measurement, the liquid sample 12 is introduced into the capillary via the through hole 11 by a capillary suction phenomenon (see FIGS. 9 and 10), and the reaction reagent section 9 dissolves to cause an oxidation-reduction reaction. At this time, when a voltage is applied to the measurement electrode 4 and the counter electrode 5 via the terminals 2 and 3, a current is obtained, and the components and the like of the liquid sample 12 are measured.
[0004]
Further, in the production of the electrode system as described above, instead of patterning the conductive paste by screen printing, a conductive film is formed on the entire surface of the insulating substrate 1, and a cut is made on the surface with a blade to form the conductive film. There is also a structure in which the measurement electrode 4 and the counter electrode 5 and the terminal portions 2 and 3 are divided (FIG. 11). In the biosensor of the type in which the conductive film formed on the entire surface is divided by the groove 13, there is also a biosensor in which the conductive film is formed on the entire surface by vapor deposition, sputtering, or bonding a metal foil. Irradiation and division are also performed. The through-hole 11 of the biosensor shown in FIG. 11 functions as an air hole, and the liquid sample 12 is introduced into the capillary from the side of the band-shaped space 8 by a capillary suction phenomenon.
[0005]
[Problems to be solved by the invention]
However, with the above configuration alone, there is a case where the liquid sample 12 is not sucked even if it is spotted on the entrance of the capillary. In particular, when blood is used, the viscosity of the liquid sample 12 is increased by components such as blood cells, proteins, and lipids, causing a phenomenon in which the liquid resistance increases and capillary suction does not proceed. When such a suction failure of the liquid sample 12 occurs, the precision and accuracy of the measured value are not reliable, and the measurer must take measures other than discarding this biosensor and replacing it with another new biosensor. Therefore, there is a problem that a heavy burden is imposed on the user.
[0006]
In order to smoothly guide the liquid sample 12 into the capillary, a surfactant is dispensed into the band-shaped space 8 formed by the spacer 7. There is also a case where the liquid sample 12 is not sufficiently diffused and is not sufficiently widened and dried, and in such a case, the suction failure of the liquid sample 12 also occurs.
[0007]
Therefore, an object of the present invention is to solve the above-mentioned problems, and a method of manufacturing a biosensor and a biosensor capable of accurately sucking a liquid sample into a capillary and performing precise and accurate measurement. Is provided.
[0008]
[Means for Solving the Problems]
In order to achieve the above object, the present invention has an electrode system including at least a measurement electrode and a counter electrode provided on an insulating substrate, and is overlapped so as to form a space by partially facing the electrode system. It has a spacer, a reaction reagent portion formed on an insulating substrate including an electrode system in a space area, and a cover plate superimposed on the spacer, and a space surrounded by the insulating substrate, the spacer, and the cover plate. In a biosensor forming a capillary as a liquid sample passage, a hydrophilic resin layer is entirely formed on a surface of an insulating substrate on which an electrode system is formed, and an electroless plating layer is formed on the hydrophilic resin layer. The electrode system was formed such that the hydrophilic resin layer was exposed around the pattern of the electrode system.
[0009]
Further, the present invention provides an electrode system comprising at least a measurement electrode and a counter electrode provided on an insulating substrate, a spacer overlapped so as to form a space by partially facing the electrode system, and a space inside the space. A reaction reagent portion formed on an insulating substrate including the electrode system of (1) and a cover plate overlaid on a spacer, and a space surrounded by the insulating substrate, the spacer, and the cover plate is a liquid sample passage. In the biosensor forming
A hydrophilic resin layer is entirely formed on the surface of the insulating substrate on which the electrode system is formed, and an electrode system is formed by sequentially laminating an electroless plating layer and an electroplating layer on the hydrophilic resin layer, The structure was such that the hydrophilic resin layer was exposed around the electrode system pattern.
[0010]
Further, the present invention provides a step of forming an electrode system comprising at least a measurement electrode and a counter electrode on an insulating substrate, a step of overlapping spacers so as to form a space partly facing the electrode system, Forming a reaction reagent portion on an insulating substrate including an electrode system in the region, and laminating a cover plate on a spacer, wherein a space surrounded by the insulating substrate, the spacer, and the cover plate is a liquid sample passage. In the method of manufacturing a biosensor formed to be a capillary, the step of forming an electrode system includes forming an entire surface of a hydrophilic resin layer on an insulating substrate, and forming an electroless plating layer on the hydrophilic resin layer. After forming the entire surface, an etching resist layer of a desired pattern is formed on the electroless plating layer by photolithography, and unnecessary portions of the electroless plating layer are removed by etching. Around the pattern of the electrode system to expose the hydrophilic resin layer, followed by configured it is to remove the etching resist layer.
[0011]
Further, the present invention provides a step of forming an electrode system comprising at least a measurement electrode and a counter electrode on an insulating substrate, a step of overlapping spacers so as to form a space partly facing the electrode system, Forming a reaction reagent portion on an insulating substrate including an electrode system in the region, and laminating a cover plate on a spacer, wherein a space surrounded by the insulating substrate, the spacer, and the cover plate is a liquid sample passage. In the method of manufacturing a biosensor formed to be a capillary, the step of forming an electrode system includes forming an entire surface of a hydrophilic resin layer on an insulating substrate, and forming an electroless plating layer on the hydrophilic resin layer. And after sequentially laminating the entire surface of the electroplating layer, an etching resist layer of a desired pattern is formed on the electroplating layer by photolithography, and an unnecessary portion of the electroless plating layer and Care plating layer around the pattern of the electrode system is removed by etching to expose the hydrophilic resin layer, followed by configured it is to remove the etching resist layer.
[0012]
In each of the above configurations, the hydrophilic resin layer is configured to be one selected from a vinyl alcohol resin, an acrylic resin, and a cellulose resin.
[0013]
BEST MODE FOR CARRYING OUT THE INVENTION
Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. FIG. 1 is an exploded perspective view showing one embodiment of the biosensor according to the present invention, FIGS. 2 to 6 are cross-sectional views showing one embodiment of an electrode forming process in the biosensor according to the present invention, and FIG. It is a partial sectional view of a biosensor. In the figure, 1 is an insulating substrate, 2 and 3 are terminal portions, 4 is a measurement electrode, 5 is a counter electrode, 7 is a spacer, 8 is a space portion, 9 is a reaction reagent portion, 10 is a cover plate, 12 is a liquid sample, Reference numeral 14 denotes an electroless plating layer, 15 denotes a hydrophilic resin layer, 16 denotes an etching resist layer, and 17 denotes a photosensitive resist film.
[0014]
The biosensor of the present invention includes an electrode system provided on the insulating substrate 1 and including at least the measurement electrode 4 and the counter electrode 5, and a spacer overlapped so as to form a space 8 with a part of the electrode system facing the electrode system. 7, a reaction reagent portion 9 formed on the insulating substrate 1 including the electrode system in the space 8, and a cover plate 10 superposed on the spacer 7, and the insulating substrate 1, the spacer 7, and the cover plate The space surrounded by 10 forms a capillary which is a liquid sample passage. The feature of the capillary is that a hydrophilic resin layer 15 is formed on the surface of the insulating substrate 1 on which the electrode system is formed as shown in FIG. An electrode system composed of the electroless plating layer 14 is formed on the entire surface of the hydrophilic resin layer 15, and the hydrophilic resin layer 15 is exposed around the electrode system pattern. By the exposed surface of the hydrophilic resin layer 15, the biosensor of the present invention can guide the liquid sample 12 smoothly into the capillary.
[0015]
In order to obtain such a biosensor, the following is performed.
[0016]
First, an electrode system including at least the measurement electrode 4 and the counter electrode 5 is formed on the insulating substrate 1. Specifically, after the hydrophilic resin layer 15 is entirely formed on the insulating substrate 1 and the electroless plating layer 14 is entirely formed on the hydrophilic resin layer 15 (see FIG. 2), An etching resist layer 16 having a desired pattern is formed on the plating layer 14 by photolithography (see FIG. 3), and unnecessary portions of the electroless plating layer 14 are removed by etching (see FIG. 4) to form an electrode pattern. The hydrophilic resin layer 15 is exposed to the periphery (see FIG. 5), and then the etching resist layer 16 is removed (see FIG. 6).
[0017]
The material, thickness and the like of the insulating substrate 1 are not particularly limited, but a plastic film such as polyethylene terephthalate can be used because the hydrophilic resin layer can be coated at low cost.
[0018]
The resin layer formed on the insulating substrate 1 needs to be hydrophilic in order to form electroless plating with good adhesion. In addition, since the unnecessary electroless plating layer 14 is removed by etching, the surface of the hydrophilic resin layer 15 is finally exposed to form one surface of the capillary (see FIG. 7). Good wetting with the liquid sample 12. Therefore, it is not necessary to dispense and form a surfactant later, and since the hydrophilic resin layer 15 is formed entirely on the insulating substrate 1, the liquid sample 12 can be reliably sucked into the capillary. it can.
[0019]
As the hydrophilic resin used for the hydrophilic resin layer 15, a vinyl alcohol resin, an acrylic resin, a cellulose resin, or the like is appropriate. For example, as the vinyl alcohol-based resin, an ethylene-vinyl alcohol copolymer, a vinyl acetate-vinyl alcohol copolymer, or the like is preferable. In addition, as the acrylic resin, polyhydroxyethyl acrylate, polyhydroxypropyl acrylate, polyhydroxyethyl methacrylate, polyhydroxypropyl methacrylate, polyacrylamide, polymethylolacrylamide, or a copolymer thereof is preferable. Further, as the cellulosic resin, nitrocellulose, acetylpropylcellulose, acetylbutylcellulose and the like are preferable. Means for forming the hydrophilic resin layer 15 is not particularly limited as long as the hydrophilic resin layer 15 can be entirely formed on the insulating substrate 1. For example, spin coating, roll coating, dipping, bar coating , Die coating and the like.
[0020]
In forming the electroless plating layer 14, first, an electroless plating nucleus for chemical plating is formed on the hydrophilic resin layer 15. Specifically, the insulating substrate 1 on which the hydrophilic resin layer 15 is formed is immersed in a chemical plating catalyst solution such as a palladium catalyst solution. In this way, the chemical plating catalyst is adsorbed on the surface of the hydrophilic resin layer 15 or impregnated in the hydrophilic resin layer 15 to form an electroless plating nucleus. The electroless plating layer 14 is formed by treating the hydrophilic resin layer 15 with the electroless plating nucleus formed thereon with an electroless plating solution. The type of metal formed as the electroless plating layer 14 is not particularly limited, and may be gold, silver, copper, nickel, platinum, palladium, rhodium, or the like, which can be electrolessly plated and used as an electrode. Just fine. Further, if necessary to obtain characteristics as an electrode, two or more kinds of metals may be laminated and plated. The chemical plating catalyst may be dissolved or dispersed in a solvent together with the hydrophilic resin when forming the hydrophilic resin layer 15.
[0021]
The thickness of the electroless plating layer 14 is preferably in the range of 0.1 to 5 μm. If the thickness is less than 0.1 μm, the conductivity may be poor, or the film may be weak and easily damaged. If the thickness is more than 5 μm, the metal material is wasted, and it is difficult to achieve high etching accuracy. In order to form a predetermined thickness in a short time, electroplating may be further performed on the electroless plating film.
[0022]
When the electrode system is not the electroless plating layer 14 alone but has an electroplating layer 18 laminated thereon, the electrode system is formed as follows. Specifically, after the hydrophilic resin layer 15 is entirely formed on the insulating substrate 1 and the electroless plating layer 14 and the electroplating layer 18 are sequentially laminated on the entire surface of the hydrophilic resin layer 15 (see FIG. 12), an etching resist layer 16 having a desired pattern is formed on the electroplating layer 18 by photolithography (see FIG. 13), and unnecessary portions of the electroless plating layer 14 and the electroplating layer 18 are etched (see FIG. 14). ) To expose the hydrophilic resin layer 15 around the electrode pattern (see FIG. 15), and then remove the etching resist layer 16 (see FIG. 16).
[0023]
The electroplating layer 18 is formed by energizing the electroless plating layer 14 in an electroplating solution using the electroless plating layer 14 as a positive electrode. The type of metal formed as the electroplating layer 18 is not particularly limited, and may be gold, silver, copper, nickel, platinum, palladium, rhodium, or the like as long as it can be electroplated and can be used as an electrode. . Further, if necessary to obtain characteristics as an electrode, two or more kinds of metals may be laminated and plated.
[0024]
Further, the total thickness of the electroplating layer 18 and the electroless plating layer 14 is preferably in the range of 0.5 to 5 μm. When the thickness is smaller than 0.5 μm, the predetermined film thickness can be formed in a sufficiently short time only by the electroless plating layer 14 without laminating the electroplating layer 18. If the thickness is more than 5 μm, the metal material is wasted, and it is difficult to improve the etching accuracy.
[0025]
The formation of the etching resist layer 16 by photolithography is performed by coating a photocurable or photodecomposable photosensitive resist film 17 on the electroless plating layer 14, superposing and exposing a mask film, and developing the mask film. The etching resist layer 16 corresponding to the above pattern is formed. The above-mentioned coating may be performed by a general coating method. Alternatively, the insulating substrate 1 on which the hydrophilic resin layer 15 and the electroless plating layer 14 are formed may be immersed in a photosensitive electrodeposition solution for electrodeposition coating. . As the material of the photosensitive resist film 17, for example, a photo-curable or photo-decomposable photosensitive resist material such as acrylic, polyvinyl cinnamate, synthetic rubber, and novolak is used. As light used for exposure, light from a sunlight, a mercury lamp, a xenon lamp, an arc lamp, an argon laser, or the like is used. When the photosensitive resist film 17 is a photo-curing type, development is performed by selectively removing uncured portions by using sodium carbonate or the like as a developing solution. When the photosensitive resist film 17 is of a photo-decomposable type, the photo-resist is performed by selectively removing the decomposed portion by using sodium metasilicate as a developing solution.
[0026]
The pattern of the etching resist layer 16 is formed according to the pattern of the electrode system. Although FIG. 1 shows a two-electrode system including only the measurement electrode 4 and the counter electrode 5, more accurate measurement is possible by using a three-electrode system including a reference electrode. Further, in FIG. 1, the electrode system pattern includes a lead having terminals 2 and 3 in addition to the measurement electrode 4 and the counter electrode 5, but these leads may be separately provided with silver paste or the like.
[0027]
In the patterning of the electrode system according to the present invention, the etching is performed using the etching resist layer 16 formed by photolithography. As compared with the case where an electrode system is formed, the dimensional accuracy of the pattern and the linearity of the pattern edge are better, and the measurement accuracy does not deteriorate due to the variation of the area of the measurement electrode. When the electrode system is patterned by screen printing, liquid dripping or bleeding occurs in the printed layer, and the dimensional accuracy of the pattern and the linearity of the pattern edge part deteriorate. In addition, when the electrode system is formed by dividing the conductive film with a blade, if the pattern of the electrode system is small and complicated, it is difficult to make a cut accurately, and the edge of the cut portion is finely cracked by the stress of the blade. As a result, the linearity of the pattern edge portion deteriorates. In the case where the electrode system is formed by dividing the conductive film by the laser processing method shown as a conventional technique, variation in the area of the measurement electrode can be considerably suppressed, but depending on the material of the substrate from the viewpoint of heat resistance. Since it cannot be used, it is still inferior to the patterning means of the present invention.
[0028]
The etching solution used for the above etching is an alkali etching solution such as ammonium persulfate, ammonium and ammonium chloride, or an acidic etching solution such as cupric chloride, ferric chloride, a mixed solution of chromic acid / sulfuric acid, and a mixed solution of hydrogen peroxide / sulfuric acid. Is appropriately selected depending on the type of metal of the electroless plating layer 14 and the electroplating layer 18. For example, if the metal of the electroless plating layer 14 and the electroplating layer 18 is nickel or copper, ferric chloride or the like may be used as an etchant. To remove the etching resist layer 16, an appropriate release agent such as acetone, methylene chloride, glycol ether, a mixed solvent thereof, or a mixed solution thereof with an aqueous alkali solution such as sodium hydroxide, potassium hydroxide, or the like is used. Use an organic solvent.
[0029]
After the electrode system including at least the measurement electrode 4 and the counter electrode 5 is formed on the insulating substrate 1 as described above, the spacer 7 is overlapped so as to form a space 8 with a part of the electrode system facing. . As a material of the spacer 7, for example, a plastic film or an ink layer having an adhesive layer formed on both surfaces can be used. The thickness of the spacer 7 is appropriately set according to the shape of the space 8, wettability, and the like.
[0030]
Next, the reaction reagent section 9 is formed on the insulating substrate 1 including the electrode system in the space 8 formed by the spacer 7. The reaction reagent section is formed by applying a reaction reagent with a dispenser or by printing such as screen printing. In order to maintain the area accuracy of the reaction reagent section, first, a reaction reagent formation section having a certain area may be defined with a resist or a double-sided tape, and then the reaction reagent may be applied or printed. Further, the reaction reagent section 9 may be formed before the spacers 7 are overlapped.
[0031]
Finally, a cover plate 10 is superimposed on the spacer 7 in order to surely guide the small amount of the liquid sample 12 to the reaction reagent portion for analysis, and the space surrounded by the insulating substrate 1, the spacer 7 and the cover plate 10 is a liquid. It is formed to be a capillary which is a sample passage. As the cover plate 10, a film of polyethylene terephthalate, acetyl cellulose, acrylic, polycarbonate, or the like may be used. In the biosensor shown in FIG. 1, the spacer 7 is formed of two parts and forms a space 8 having an opening also on the side opposite to the suction port of the liquid sample 12. The spacer 7 may form a notched space as shown in FIG. 11, in which case the cover plate 10 is provided with an air hole.
[0032]
【Example】
(Example 1) A 1% water-n-propyl alcohol mixed solution of an ethylene-vinyl alcohol copolymer was applied by dipping on the entire surface of a 250 μm-thick polyethylene terephthalate film to form a 0.5 μm-thick hydrophilic resin layer. Formed and air dried for 20 minutes. Next, it is immersed in an aqueous 18% formaldehyde solution for 5 minutes to reduce palladium chloride in the hydrophilic resin layer to form a plating nucleus. After washing with water, electroless copper plating is performed to form a 1 μm thick layer on the surface of the hydrophilic resin layer. A copper electroless plating layer was formed. Next, after applying an acrylic photocurable photosensitive resist material on the electroless plating layer to form a photosensitive resist film, exposing and exposing a mask film, developing and developing the measurement electrode and the counter electrode. An etching resist layer having an electrode pattern was formed. Next, unnecessary copper in the non-resist part was removed by etching with a 10% cupric chloride solution to expose the hydrophilic resin layer around the electrode pattern. After the etching, the etching resist layer was completely removed by dipping in acetone. Further, a spacer was overlapped by bonding a polyethylene terephthalate film with an adhesive having a thickness of 0.2 mm so as to form a space portion so as to face a part of each electrode. The reaction reagent solution was dispensed using a dispenser on the insulating substrate including the electrode system in the space area to form a reaction reagent section. Finally, an acrylic film having a thickness of 0.1 mm as a cover plate was overlaid and adhered to the spacer to obtain a biosensor.
[0033]
(Example 2) The same procedure as in Example 1 was performed except that the thickness of the copper electroless plating layer was 0.2 µm, and a 4 µm copper electroplating layer was formed before forming the photosensitive resist film.
[0034]
When a plurality of biosensors were manufactured by the methods of Example 1 and Example 2, and blood was used as a liquid sample, and the glucose concentration was measured by each biosensor, the measurement results did not vary between lots.
[0035]
【The invention's effect】
The biosensor and the method for manufacturing a biosensor of the present invention have the following configurations, and therefore have the following excellent effects.
[0036]
That is, a hydrophilic resin layer is entirely formed on the surface of the insulating substrate on which the electrode system is formed, and an electrode system comprising an electroless plating layer, or an electroless plating layer and an electroplating layer are formed on the hydrophilic resin layer. Are sequentially laminated, and the hydrophilic resin layer is exposed around the pattern of the electrode system, so that the liquid sample can be reliably sucked into the capillary. Therefore, accurate and accurate measurement is possible.
[Brief description of the drawings]
FIG. 1 is an exploded perspective view showing one embodiment of a biosensor according to the present invention.
FIG. 2 is a cross-sectional view showing one embodiment of a process for forming an electrode in the biosensor according to the present invention.
FIG. 3 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 4 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 5 is a cross-sectional view showing one embodiment of a process for forming an electrode in the biosensor according to the present invention.
FIG. 6 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 7 is a partial cross-sectional view of the biosensor of FIG.
FIG. 8 is an exploded perspective view showing a general form of a biosensor.
FIG. 9 is a perspective view illustrating the introduction of a liquid sample into the biosensor of FIG. 8;
FIG. 10 is a cross-sectional view illustrating introduction of a liquid sample into the biosensor of FIG.
FIG. 11 is an exploded perspective view showing an example of a biosensor in which a conductive film is divided by grooves to form electrodes.
FIG. 12 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 13 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 14 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 15 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
FIG. 16 is a cross-sectional view showing one embodiment of a process of forming an electrode in the biosensor according to the present invention.
DESCRIPTION OF SYMBOLS 1 Insulating substrate 2 Terminal part 3 Terminal part 4 Measurement electrode 5 Counter electrode 6 Insulating layer 7 Spacer 8 Space part 9 Reagent part 10 Cover plate 11 Through hole 12 Liquid sample 13 Groove 14 Electroless plating layer 15 Hydrophilic resin layer 16 Etching Resist layer 17 Photosensitive resist film 18 Electroplating layer

Claims (6)

An electrode system including at least a measurement electrode and a counter electrode provided on an insulating substrate, a spacer overlapped so as to form a space by partially facing the electrode system, and an insulation including the electrode system in the space area A bioreactor having a reaction reagent portion formed on an insulating substrate and a cover plate superimposed on a spacer, wherein a space surrounded by the insulating substrate, the spacer and the cover plate forms a capillary which is a liquid sample passage. In the sensor,
A hydrophilic resin layer is entirely formed on the surface of the insulating substrate on which the electrode system is formed, and an electrode system including an electroless plating layer is formed on the hydrophilic resin layer. A biosensor characterized in that a conductive resin layer is exposed. An electrode system including at least a measurement electrode and a counter electrode provided on an insulating substrate, a spacer overlapped so as to form a space by partially facing the electrode system, and an insulation including the electrode system in the space area A bioreactor having a reaction reagent portion formed on an insulating substrate and a cover plate superimposed on a spacer, wherein a space surrounded by the insulating substrate, the spacer and the cover plate forms a capillary which is a liquid sample passage. In the sensor,
A hydrophilic resin layer is entirely formed on the surface of the insulating substrate on which the electrode system is formed, and an electrode system is formed by sequentially laminating an electroless plating layer and an electroplating layer on the hydrophilic resin layer, A biosensor characterized in that a hydrophilic resin layer is exposed around an electrode pattern. The biosensor according to claim 1, wherein the hydrophilic resin layer is one selected from a vinyl alcohol resin, an acrylic resin, and a cellulose resin. A step of forming an electrode system comprising at least a measurement electrode and a counter electrode on an insulating substrate; a step of facing a part of the electrode system to overlap a spacer so as to form a space; and an electrode system in a space area. A step of forming a reaction reagent section on the insulating substrate, and a step of laminating a cover plate on the spacer so that a space surrounded by the insulating substrate, the spacer, and the cover plate becomes a capillary serving as a liquid sample passage. In the method for producing a biosensor formed in,
The step of forming the electrode system includes forming a hydrophilic resin layer entirely on the insulating substrate, forming an electroless plating layer entirely on the hydrophilic resin layer, and then performing photolithography on the electroless plating layer. Forming an etching resist layer of a desired pattern by etching, removing an unnecessary portion of the electroless plating layer by etching to expose the hydrophilic resin layer around the electrode system pattern, and thereafter removing the etching resist layer. A method for producing a biosensor, the method comprising: A step of forming an electrode system comprising at least a measurement electrode and a counter electrode on an insulating substrate; a step of facing a part of the electrode system to overlap a spacer so as to form a space; and an electrode system in a space area. A step of forming a reaction reagent section on the insulating substrate, and a step of laminating a cover plate on the spacer so that a space surrounded by the insulating substrate, the spacer, and the cover plate becomes a capillary serving as a liquid sample passage. In the method for producing a biosensor formed in,
The step of forming the electrode system is such that a hydrophilic resin layer is entirely formed on the insulating substrate, and an electroless plating layer and an electroplating layer are sequentially laminated on the hydrophilic resin layer over the entire surface. Form an etching resist layer of a desired pattern by photolithography on it, remove the unnecessary portions of the electroless plating layer and the electroplating layer by etching to expose the hydrophilic resin layer around the electrode system pattern, and then A method for producing a biosensor, which comprises removing an etching resist layer. The method for producing a biosensor according to claim 4, wherein the hydrophilic resin layer is one selected from a vinyl alcohol resin, an acrylic resin, and a cellulose resin.

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