WO2023120326A1

WO2023120326A1 - Biosensor

Info

Publication number: WO2023120326A1
Application number: PCT/JP2022/046055
Authority: WO
Inventors: 聡太近藤; 千春小田根
Original assignee: 日東電工株式会社
Priority date: 2021-12-20
Filing date: 2022-12-14
Publication date: 2023-06-29

Abstract

The biosensor according to the present invention is provided with a sensor main body which acquires biological information, an electrode which is connected to the sensor main body and has adhesiveness, a first layer member in which the electrode is provided on the lower surface thereof, and a second layer member which is adhered in such a manner that the electrode is exposed on the lower surface of the first layer member and the sensor main body is covered, in which an adhesion surface to a living body is formed by the electrode and the second layer member.

Description

biosensor

The present invention relates to biosensors.

Medical institutions such as hospitals and clinics, nursing homes, and homes use biosensors that measure biometric information such as electrocardiogram waveforms, pulse waves, electroencephalograms, and electromyograms. A biosensor is equipped with a bioelectrode that acquires the biometric information of a subject by contacting the subject's body. make contact. Biological information is measured by acquiring an electrical signal related to the biological information with a biological electrode.

Such a biosensor includes, for example, a pressure-sensitive adhesive layer having an adhesive surface to be attached to a subject, and an electrode composed of a conductive polymer and exposed through a hole in the adhesive surface. is attached to the skin, a biosensor that acquires biometric information with electrodes exposed through holes in the attached surface is disclosed (see, for example, Patent Document 1).

Japanese Patent Application Laid-Open No. 2020-156692

However, in the biosensor of Patent Literature 1, since the electrodes do not have adhesiveness, while the biosensor of Patent Literature 1 is attached to a biological surface such as the skin of a subject and used, a part of the electrode is attached to the biological surface. may not be able to maintain a low impedance between the biosensor and the biosurface. Further, in the biosensor disclosed in Patent Document 1, the pressure-sensitive adhesive layer must be provided around the electrodes on the lower surface of the biosensor.

Since biosensors are often used for a long time by being attached to a living body surface such as the skin of a subject, in order to stably acquire electrical signals related to biometric information for a long time, a smaller biosensor and a biosensor are required. It is important to be able to maintain a low impedance to the surface.

An object of one aspect of the present invention is to provide a biosensor that is smaller and that can maintain a state of low contact impedance with the surface of a living body.

One aspect of the biosensor according to the present invention includes a sensor main body that acquires biometric information, an adhesive electrode connected to the sensor main body, a first layer member provided with the electrode on the lower surface, and the first a second layer member that exposes the electrodes on the bottom surface of the layer member and is attached so as to cover the sensor body, and the electrodes and the second layer member form a surface to be attached to the living body. .

One aspect of the biosensor according to the present invention is smaller and can maintain a low contact impedance with the surface of the living body.

BRIEF DESCRIPTION OF THE DRAWINGS It is a perspective view which shows the whole structure which shows the biosensor which concerns on embodiment of this invention. FIG. 4 is a plan view showing an example of each part of the biosensor; FIG. 2 is a cross-sectional view in the longitudinal direction of the biosensor, and is a cross-sectional view taken along line II of FIG. 1; 1. It is explanatory drawing which shows the state which affixed the biosensor of FIG. 1 on the chest of the living body.

Hereinafter, embodiments of the present invention will be described in detail. In addition, in order to facilitate understanding of the description, the same components are denoted by the same reference numerals in each drawing, and overlapping descriptions are omitted. Also, the scale of each member in the drawings may differ from the actual scale. Unless otherwise specified, "-" indicating a numerical range in this specification includes the numerical values described before and after it as lower and upper limits.

<Biological sensor>
A biosensor according to this embodiment will be described. The living body refers to the human body (person) and animals such as cows, horses, pigs, chickens, dogs and cats. The biosensor according to this embodiment can be suitably used for a living body, especially for the human body. In this embodiment, as an example, a case where the living body is a person will be described.

The biosensor according to this embodiment is a patch-type biosensor that measures biometric information by attaching it to a part of a living body (for example, skin, scalp, forehead, etc.). In this embodiment, a case will be described in which a biosensor is attached to a person's skin and measures an electrical signal (biological signal) relating to the person's biometric information.

FIG. 1 is a perspective view showing the overall configuration of the biosensor according to this embodiment. The left side of FIG. 1 shows the appearance of the biosensor according to the present embodiment, and the right side of FIG. 1 shows the disassembled state of each part of the biosensor according to the present embodiment. FIG. 2 is a plan view showing an example of each part of the biosensor. FIG. 3 is a cross-sectional view in the longitudinal direction of the biosensor, which is a cross-sectional view taken along line II of FIG.

As shown in FIGS. 1 and 2, the biosensor 1 is a plate-like (sheet-like) member formed in a substantially elliptical shape in plan view. As shown in FIGS. 2 and 3, the biosensor 1 has a first layer member 10, an adhesive electrode 20, a sensor section 30 and a second layer member 40. The first layer member 10, the adhesive electrode 20 and It is formed by laminating the second layer member 40 in this order from the first layer member 10 side toward the second layer member 40 side. The adhesive electrodes 20 are provided near both ends of the surface of the first layer member 10 on the sticking side (−Z axis direction) to the skin 2 . The sensor section 30 is installed on the second layer member 40 and accommodated in the storage space S formed by the first layer member 10 . In the biosensor 1, the adhesive electrode 20 and the second layer member 40 form a sticking surface to the skin 2 of the living body. The biosensor 1 attaches the adhesive electrode 20 and the second layer member 40 to the skin 2, and measures the potential difference (polarization voltage) between the skin 2 and the adhesive electrode 20 to obtain biological information of the subject. Electrical signals (biological signals) are measured.

In FIGS. 1 to 3, a three-dimensional orthogonal coordinate system with three axial directions (X-axis direction, Y-axis direction, Z-axis direction) is used, and the lateral direction of the biosensor is defined as the X-axis direction, and the longitudinal direction thereof as the Y-axis direction. , the height direction (thickness direction) is the Z-axis direction. The opposite direction (outside) to the side where the biosensor 1 is attached to the living body (subject) (adhering side) is the +Z-axis direction, and the adhering side is the -Z-axis direction. In the following description, for convenience of explanation, the +Z axis direction may be referred to as the upper side or the upper side, and the -Z axis direction may be referred to as the lower side or the lower side, but this does not represent a universal vertical relationship.

The biological signal is, for example, an electrical signal representing an electrocardiogram waveform, an electroencephalogram, a pulse, or the like.

When using the biosensor 1, the inventor of the present application focused on making the electrodes themselves sticky. The inventors of the present application have found that by directly attaching the adhesive electrode 20 having adhesiveness to the lower surface of the upper sheet 12, the adhesion state to the upper sheet 12 can be maintained and the adhesion to the living body surface can be improved. It has been found that the biosensor 1 can be made smaller and the contact impedance with the surface of the living body can be reduced.

[First layer member]
As shown in FIGS. 1 and 2, the first layer member 10 includes a cover member 11 and an upper sheet 12 laminated in this order. The cover member 11 and the upper sheet 12 have substantially the same outer shape in plan view.

(Cover member)
As shown in FIG. 3 , the cover member 11 is positioned on the outermost side (+Z-axis direction) of the biosensor 1 and adhered to the upper surface of the upper sheet 12 . The cover member 11 has a central portion in the longitudinal direction (Y-axis direction) of which a protruding portion 111 protrudes substantially like a dome in the height direction (+Z-axis direction) of FIG. It has

flat portions

112A and 112B provided on both end sides in the axial direction. The top and bottom surfaces of the protrusion 111 and the top and bottom surfaces of the

flat portions

112A and 112B may be flat.

The cover member 11 has a depression 111a formed in a concave shape on the living body side on the inner side (attachment side) of the projecting portion 111 . A recess 111 a on the inner surface of the protrusion 111 , the adhesive electrode 20 and the second layer member 40 form a storage space S for storing the sensor section 30 inside the protrusion 111 (adhering side).

As a material for forming the cover member 11, for example, a flexible material such as silicone rubber, fluororubber, or urethane rubber can be used. Alternatively, the cover member 11 may be formed by using a base resin such as polyethylene terephthalate (PET) as a support and laminating the flexible material on the surface of the support. By forming the cover member 11 using the above flexible material or the like, the sensor unit 30 arranged in the storage space S of the cover member 11 is protected, and the impact applied to the biosensor 1 from the upper surface side is protected. is absorbed and the impact applied to the sensor section 30 is softened.

The thickness of the upper surface and side walls of the protruding portion 111 may be thicker than the thickness of the

flat portions

112A and 112B. As a result, the flexibility of the projecting portion 111 can be made lower than that of the

flat portions

112A and 112B, and the sensor portion 30 can be protected from external forces applied to the biosensor 1. FIG.

The thickness of the upper surface and sidewalls of the projecting portion 111 can be appropriately designed, and may be, for example, 1.5 mm to 3 mm. The thickness of the

flat portions

112A and 112B can also be appropriately designed, and may be, for example, 0.5 mm to 1 mm.

Since the thin

flat portions

112A and 112B are more flexible than the protruding portion 111, when the biosensor 1 is attached to the skin 2, the surface of the skin 2 is affected by body movements such as stretching, bending, and twisting. It is easy to deform following deformation. Thereby, when the surface of the skin 2 is deformed, the stress applied to the

flat portions

112A and 112B can be alleviated, and the biosensor 1 can be made difficult to peel off from the skin 2 .

The outer peripheral portions of the

flat portions

112A and 112B may have a shape in which the thickness gradually decreases toward the ends. As a result, the flexibility of the outer peripheral portions of the

flat portions

112A and 112B can be further increased, and the biosensor 1 can be attached to the skin 2 more easily than when the thickness of the outer peripheral portions of the

flat portions

112A and 112B is not reduced. It is possible to improve the feeling of wearing when it is worn.

The hardness (strength) of the cover member 11 can be appropriately designed to any size, for example, 40-70. If the hardness of the cover member 11 is within the above preferred range, the upper sheet 12, the adhesive electrode 20 and the second layer member 40 will not be affected by the cover member 11 when the skin 2 is stretched due to body movement. can be easily deformed according to the movement of the skin 2. The hardness (hardness) refers to Shore A hardness.

(upper sheet)
As shown in FIG. 3, the upper sheet 12 is adhered to the lower surface of the cover member 11 . The upper sheet 12 has a through hole 12a at a position facing the projecting portion 111 of the cover member 11 . The through hole 12 a allows the sensor body 32 of the sensor unit 30 to be stored in the storage space S formed by the recess 111 a on the inner surface of the cover member 11 and the through hole 12 a without being blocked by the upper sheet 12 .

The upper sheet 12 includes a first base material 121 and an upper adhesive layer 122 provided on the upper surface of the first base material 121, which are laminated in this order.

((first base material))
The first base material 121 is formed in a sheet shape. The first base material 121 has a porous structure and may be formed using a flexible, waterproof, and moisture-permeable porous body. As the porous body, for example, a foam material (foam) having a cell structure such as continuous cells, closed cells, semi-closed cells, etc. can be used. As a result, water vapor generated by sweat or the like generated from the skin 2 to which the biosensor 1 is attached can be released to the outside of the biosensor 1 through the first base material 121 .

The moisture permeability of the first base material 121 is preferably 100 (g/m ² ·day) to 5000 (g/m ² ·day). By setting the moisture permeability of the first base material 121 to 100 (g/m ² ·day) to 5000 (g/m ² ·day), the first base material 121 can absorb water vapor entering from one surface side to the first It can pass through the base material 121 and be stably emitted from the other side.

Thermoplastic resins such as polyurethane resins, polystyrene resins, polyolefin resins, silicone resins, acrylic resins, vinyl chloride resins, and polyester resins can be used as materials for forming the first base material 121, for example. can be done. As the first base material 121, for example, FOLEC manufactured by INOAC Corporation can be used.

The thickness of the first base material 121 can be set as appropriate, and may be, for example, 0.5 mm to 1.5 mm.

The first base material 121 has a through hole 121a at a position facing the projecting portion 111 of the cover member 11 . By providing the upper adhesive layer 122 on the surface of the first base material 121 other than the through-holes 121a, the upper adhesive layer 122 can also be formed with the through-holes 122a. The through hole 12a is formed by the through hole 121a and the through hole 122a.

Note that the first base material 121 may be a base material that does not have a porous structure as long as it has flexibility, waterproofness, and moisture permeability. Since the first base material 121 is flexible, waterproof, and moisture-permeable, the first base material 121 can easily extend in contact with the skin 2 and can maintain contact with the skin 2. Intrusion of liquid into the gap between the base material 121 and the upper adhesive layer 122 can be suppressed. In addition, water vapor generated by sweat or the like generated from the skin 2 to which the biosensor 1 is attached can be released to the outside of the biosensor 1 through the first base material 121 . Therefore, the upper sheet 12 can easily maintain its durability.

As the material of the base material having no porous structure, as mentioned above, for example, heat-resistant resin such as polyurethane-based resin, polystyrene-based resin, polyolefin-based resin, silicone-based resin, acrylic-based resin, vinyl chloride-based resin, polyester-based resin, etc. A plastic resin can be used.

((Adhesive layer for upper part))
As shown in FIG. 3 , the upper adhesive layer 122 is attached to the upper surface of the first base material 121 . The upper adhesive layer 122 is adhered to a position on the upper surface of the first base material 121 corresponding to the flat surface on the adhered side (−Z axis direction) of the cover member 11, and the first base material 121 and the cover are attached. It has a function of adhering to the member 11 .

As a material for forming the upper adhesive layer 122, a silicone-based adhesive, a silicone tape, or the like can be used.

The thickness of the upper adhesive layer 122 can be set as appropriate, and can be, for example, 10 μm to 300 μm.

[Adhesive electrode]
As shown in FIG. 3, the adhesive electrode 20 is attached to the lower surface of the upper sheet 12, which is the attachment side (-Z axis direction). The adhesive electrode 20 is sandwiched between the

terminal portions

332A and 332B and the lower adhesive layer 42 of the second layer member 40 on the lower surface of the first base material 121. affixed in place. A portion of the adhesive electrode 20 that is not sandwiched between the upper sheet 12 and the lower adhesive layer 42 contacts the skin 2 . When the biosensor 1 is attached to the skin 2, the biosignal can be detected by the adhesive electrode 20 coming into contact with the skin 2. FIG. Note that the adhesive electrode 20 may be embedded in the second base material 41 and the lower adhesive layer 42 of the second layer member 40 while being exposed so as to be in contact with the skin 2 .

The adhesive electrode 20 is composed of a pair of

adhesive electrodes

20A and 20B. As shown in FIG. 3, the adhesive electrode 20A is arranged on the left side in the drawing, and the adhesive electrode 20B is arranged on the right side in the drawing. One end side (inner side) of the adhesive electrode 20A in the longitudinal direction (Y-axis direction) is in contact with the terminal portion 332A. The portion 332B is contacted. A pair of

adhesive electrodes

20A and 20B have substantially the same shape.

One end side of the adhesive electrode 20A that contacts the terminal section 332A of the sensor section 30 and one end side of the adhesive electrode 20B that contacts the terminal section 332B of the sensor section 30 are defined as the facing portion 20a. A portion of the adhesive electrode 20A that does not contact the terminal portion 332A and a portion of the adhesive electrode 20B that does not contact the terminal portion 332B (the other end (outer side) in the longitudinal direction (Y-axis direction)) are exposed portions 20b.

The adhesive electrode 20 is an electrode having adhesiveness, and is formed using an adhesive electrode sheet in which an adhesive conductive composition containing a conductive polymer, a binder resin, and a moisturizing agent is formed into a sheet. can.

Examples of conductive polymers include polythiophene-based conductive polymers, polyaniline-based conductive polymers, polypyrrole-based conductive polymers, polyacetylene-based conductive polymers, polyphenylene-based conductive polymers, derivatives thereof, and derivatives thereof. can be used. These may be used individually by 1 type, and may be used together 2 or more types. Among these, it is preferable to use a composite of polythiophene doped with polyaniline as a dopant. Among the composites of polythiophene and polyaniline, poly3,4-ethylenedioxythiophene (PEDOT) and polystyrene sulfonic acid (poly4-styrene sulfonate It is more preferable to use PEDOT/PSS doped with phosphate (PSS).

The binder resin consists of a water-based emulsion adhesive. The water-based emulsion adhesive has the function of improving the adhesiveness and flexibility of the adhesive electrode 20 . Therefore, by including the water-based emulsion adhesive in the adhesive electrode 20, the adhesive electrode 20 can be made to have a low elasticity, and the ability to follow the irregularities on the surface of the living body can be improved.

An acrylic emulsion pressure-sensitive adhesive can be used as the water-based emulsion pressure-sensitive adhesive.

For the acrylic emulsion pressure-sensitive adhesive, it is preferable to use a silane-based emulsion pressure-sensitive adhesive containing a water-dispersible copolymer and an organic liquid component compatible with the water-dispersible copolymer.

A water-dispersible copolymer is a polymer obtained by copolymerizing a monomer mixture containing an (meth)acrylic acid alkyl ester with a silane-based monomer that can be copolymerized with the (meth)acrylic acid alkyl ester. be.

The monomer mixture containing (meth)acrylic acid alkyl ester is a monomer mixture containing (meth)acrylic acid alkyl ester as a main component, preferably 50 wt % to 100 wt %.

As the (meth)acrylic acid alkyl ester, a linear or branched alkyl ester having an alkyl group having 1 to 15 carbon atoms, preferably 1 to 9 carbon atoms is used. Specifically, for example, methyl (meth)acrylate, ethyl (meth)acrylate, n-butyl (meth)acrylate, isobutyl (meth)acrylate, pentyl (meth)acrylate, hexyl (meth)acrylate , heptyl (meth)acrylate, n-octyl (meth)acrylate, isooctyl (meth)acrylate, 2-ethylhexyl (meth)acrylate, n-nonyl (meth)acrylate, isononyl (meth)acrylate, ( Examples include (meth)acrylic acid alkyl esters having a linear or branched alkyl group such as decyl methacrylate, undecyl (meth)acrylate, and tridecyl (meth)acrylate. These can be used individually or in combination of 2 or more types.

The monomer mixture containing the (meth)acrylic acid alkyl ester may contain a carboxyl group-containing monomer copolymerizable with the (meth)acrylic acid alkyl ester.

The carboxyl group-containing monomer copolymerizable with the (meth)acrylic acid alkyl ester is a polymerizable compound containing a carboxyl group in its structure and is copolymerizable with the (meth)acrylic acid alkyl ester. Examples include (meth)acrylic acid, itaconic acid, maleic acid, maleic anhydride, 2-methacryloyloxyethylsuccinic acid, and the like. Acrylic acid is particularly preferred.

The carboxyl group-containing monomer is 0.1 wt% with respect to 100 wt% of the monomer mixture containing the (meth)acrylic acid alkyl ester from the viewpoint of hydrolysis of the silane-based monomer and adjustment of the resulting adhesiveness. It is preferable to contain ~10 wt%.

The silane-based monomer copolymerizable with the (meth)acrylic acid alkyl ester is not particularly limited as long as it is a polymerizable compound having a silicon atom and is copolymerizable with the (meth)acrylic acid alkyl ester. However, silane compounds having a (meth)acryloyl group, such as (meth)acryloyloxyalkylsilane derivatives, are preferred because of their excellent copolymerizability with (meth)acrylic acid alkyl esters. Silane-based monomers include, for example, 3-(meth)acryloyloxypropyltrimethoxysilane, 3-(meth)acryloyloxypropyltriethoxysilane, 3-(meth)acryloyloxypropylmethyldimethoxysilane, 3-(meth) ) acryloyloxypropylmethyldiethoxysilane and the like. These silane-based monomers can be used alone or in combination of two or more.

Examples of silane monomers other than the above include vinyltrimethoxysilane, vinyltriethoxysilane, 4-vinylbutyltrimethoxysilane, 4-vinylbutyltriethoxysilane, 8-vinyloctyltrimethoxysilane, 8 -vinyloctyltriethoxysilane, 10-methacryloyloxydecyltrimethoxysilane, 10-acryloyloxydecyltrimethoxysilane, 10-methacryloyloxydecyltriethoxysilane, 10-acryloyloxydecyltriethoxysilane, and the like can also be used.

The silane-based monomer is added to the monomer mixture containing the (meth)acrylic acid alkyl ester in an amount of 0.005 wt% to 2 wt% with respect to 100 wt% of the monomer mixture containing the (meth)acrylic acid alkyl ester. Polymerization is preferred.

When the silane-based monomer is copolymerized with the monomer mixture containing the (meth)acrylic acid alkyl ester, the silane compound serving as a cross-linking point can be evenly present in the molecules of the resulting copolymer. becomes. As a result, even though the water-based emulsion pressure-sensitive adhesive is a water-dispersed type, the inside and outside of the water-based emulsion pressure-sensitive adhesive particles are uniformly cross-linked, so the cohesive force is excellent, and the addition of the organic liquid component reduces skin irritation. In addition to being durable, it also has excellent fixation and sweat resistance.

The water-dispersible copolymer is obtained by copolymerizing a monomer copolymerizable with a (meth)acrylic acid alkyl ester other than the silane-based monomer and the carboxyl group-containing monomer, if necessary. may be A monomer that can be copolymerized with a (meth)acrylic acid alkyl ester other than the silane-based monomer and the carboxyl group-containing monomer is used to prevent cohesion of the adhesive electrode 20 when the water-based emulsion adhesive is formed into a sheet or the like. It can be used for the purpose of adjusting force, improving compatibility with organic liquid components, etc., and the amount used is arbitrarily set according to the purpose by replacing part of the content of the (meth)acrylic acid alkyl ester. can.

Examples of monomers copolymerizable with (meth)acrylic acid alkyl esters other than silane-based monomers and carboxyl group-containing monomers include styrenesulfonic acid, allylsulfonic acid, sulfopropyl (meth)acrylate, ( sulfoxyl group-containing monomers such as meth) acryloyloxynaphthalene sulfonic acid and acrylamidomethylpropane sulfonic acid; hydroxyl group-containing monomers such as (meth)acrylic acid hydroxyethyl ester and (meth)acrylic acid hydroxypropyl ester; ) Acrylamide, dimethyl (meth) acrylamide, N-butylacrylamide, N-methylol (meth) acrylamide, N-methylolpropane (meth) amide group-containing monomers such as acrylamide, (meth) acrylic acid aminoethyl ester, (meth ) acrylic acid dimethylaminoethyl ester, (meth)acrylic acid alkylaminoalkyl ester such as (meth)acrylic acid tert-butylaminoethyl ester, (meth)acrylic acid methoxyethyl ester, (meth)acrylic acid ethoxyethyl ester, etc. (Meth)acrylate alkoxyalkyl ester, (meth)acrylate methoxyethylene glycol ester, (meth)acrylate tetrahydrofurfuryl ester, (meth)acrylate methoxyethylene glycol ester, (meth)acrylate methoxydiethylene glycol ester, (meth)acrylate ) Alkoxy group (or ether bond in side chain) containing (meth)acrylic acid ester such as methoxypolyethylene glycol acrylate, (meth)acrylate methoxypolypropylene glycol ester, (meth)acrylonitrile, vinyl acetate, vinyl propionate, N -vinyl monomers such as vinyl-2-pyrrolidone, methylvinylpyrrolidone, vinylpyridine, vinylpiperidine, vinylpyrimidine, vinylpiperazine, vinylpyrazine, vinylpyrrole, vinylimidazole, vinylcaprolactam, vinyloxazole, and vinylmorpholine; be done. These can be used individually or in combination of 2 or more types.

The water-dispersible polymer can be obtained, for example, by subjecting a mixture of a monomer mixture containing an (meth)acrylic acid alkyl ester and a silane-based monomer to ordinary emulsion polymerization to obtain a (meth)acrylic acid alkyl ester copolymer. It can be prepared as an aqueous dispersion of the coalescence.

General batch polymerization, continuous dropping polymerization, divided dropping polymerization, etc. can be adopted as the polymerization method, and the polymerization temperature is, for example, 20°C to 100°C.

The polymerization initiator used for polymerization is not particularly limited, and common components used as polymerization initiators can be used.

A chain transfer agent may be used in the polymerization to adjust the degree of polymerization. The chain transfer agent is not particularly limited, and common components used as chain transfer agent weights can be used.

In addition to the above method, the water-dispersible copolymer is produced by obtaining a copolymer of a monomer mixture containing a (meth)acrylic acid ester and a silane-based monomer by a method other than emulsion polymerization, followed by addition of an emulsifier to water. It may be prepared by dispersing in

The organic liquid component contained in the acrylic emulsion pressure-sensitive adhesive is blended with the water-dispersible copolymer to maintain good adhesion to the biological surface, reduce keratin damage during peeling, and reduce pain during peeling. can also be reduced.

The organic liquid component is preferably liquid at room temperature and has good compatibility with the water-dispersible copolymer. The term "compatible" means that the organic liquid component is uniformly dissolved and incorporated into the water-dispersed copolymer, and refers to a state in which separation cannot be visually confirmed.

Examples of organic liquid components include esters of monobasic or polybasic acids having 8 to 18 carbon atoms and branched alcohols having 14 to 18 carbon atoms, and unsaturated fatty acids or branched acids having 14 to 18 carbon atoms and 4 Examples include esters with alcohols having a lower valence and the like.

Examples of esters of monobasic or polybasic acids having 8 to 18 carbon atoms and branched alcohols having 14 to 18 carbon atoms include isostearyl laurate, isocetyl myristate, octyldodecyl myristate, and isostearyl palmitate. , isocetyl stearate, octyldodecyl oleate, diisostearyl adipate, diisocetyl sebacate, trioleyl trimellitate, triisocetyl trimellitate and the like.

Examples of unsaturated fatty acids or branched acids having 14 to 18 carbon atoms include myristoleic acid, oleic acid, linoleic acid, linolenic acid, isopalmitic acid, and isostearic acid.

Examples of tetravalent or lower alcohols include ethylene glycol, propylene glycol, glycerin, trimethylolpropane, pentaerythritol and sorbitan.

The content of the organic liquid component can be set arbitrarily according to the types of the water-dispersible copolymer and the organic liquid component, for example, 20 wt% to 80 wt% with respect to 100 wt% of the water-dispersible copolymer. good too.

When the acrylic emulsion pressure-sensitive adhesive is a silane emulsion pressure-sensitive adhesive, the acrylic emulsion pressure-sensitive adhesive specifically includes 2-ethylhexyl acrylate, methyl methacrylate, acrylic acid and 3-methacryloxypropyltrimethoxysilane. A silane-based emulsion adhesive can be used.

Also, the acrylic emulsion pressure-sensitive adhesive may be a two-component or three-component acrylic emulsion pressure-sensitive adhesive containing a monomer mixture containing a (meth)acrylic acid alkyl ester and a carboxyl group-containing monomer. . These may contain appropriate amounts of solvents and other components within the range in which performance can be exhibited.

The monomer mixture containing the (meth)acrylic acid alkyl ester contained in the two-component or three-component acrylic emulsion pressure-sensitive adhesive is the monomer containing the (meth)acrylic acid alkyl ester contained in the above silane-based emulsion pressure-sensitive adhesive. Since it is the same as the body mixture, details are omitted.

The carboxyl group-containing monomer is preferably a carboxyl group-containing monomer copolymerizable with (meth)acrylic acid alkyl ester. The carboxyl group-containing monomer copolymerizable with the (meth)acrylic acid alkyl ester is the same as the carboxyl group-containing monomer contained in the above-mentioned monomer mixture containing the (meth)acrylic acid alkyl ester. , details are omitted.

Specifically, the two-component acrylic emulsion adhesive contains 2-ethylhexyl acrylate, which is a monomer mixture containing (meth)acrylic acid alkyl ester, and acrylic acid, which is a carboxyl group-containing monomer mixture. An adhesive can be used.

Specifically, the three-component acrylic emulsion adhesive includes 2-ethylhexyl acrylate and methyl methacrylate, which are monomer mixtures containing (meth)acrylic acid alkyl esters, and acrylic acid, which is a carboxyl group-containing monomer mixture. and can be used.

The average particle size of the water-based emulsion adhesive is preferably 100 nm to 1.0 μm, more preferably 100 nm to 500 nm, even more preferably 100 nm to 300 nm. When the average particle size is within the above preferable range, the adhesive electrode 20 can be provided with adhesive strength and water resistance.

The shape of the water-based emulsion pressure-sensitive adhesive is not particularly limited, and may be, for example, spherical, ellipsoidal, spindle-shaped, crushed, plate-shaped, or columnar.

"Average particle size" refers to the volume average particle size based on the effective diameter. The average particle size is, for example, a particle size distribution curve obtained by measuring the particle size distribution of an emulsion pressure-sensitive adhesive or an acrylic emulsion pressure-sensitive adhesive by a laser diffraction/scattering method or a dynamic light scattering method. It is the particle diameter (median diameter) when 50% by volume is accumulated from the smaller one.

The content of the binder resin is preferably 35 wt% to 90 wt%, more preferably 40 wt% to 85 wt%, even more preferably 50 wt% to 80 wt%. When the content of the binder resin is within the above preferred range, the adhesive electrode 20 can be provided with adhesive strength and flexibility, and a decrease in conductivity can be suppressed.

The moisturizing agent has the function of improving the conductivity of the adhesive electrode 20 and improving the degree of adhesion and flexibility. Moisturizers include glycerin, ethylene glycol, propylene glycol, sorbitol, polyol compounds such as these polymers N-methylpyrrolidone (NMP), dimethylformaldehyde (DMF), N—N′-dimethylacetamide (DMAc), dimethylsulfoxide and aprotic compounds such as (DMSO). These may be used individually by 1 type, and may be used together 2 or more types. Among these, glycerin is preferable from the viewpoint of compatibility with other components.

The content of the moisturizing agent is preferably 2 wt% to 60 wt%, more preferably 3 wt% to 50 wt%, and even more preferably 5 wt% to 35 wt% with respect to 100 wt% of the electrode. If the content of the humectant is within the above preferable range, the adhesive force of the adhesive electrode 20 can be improved, high adhesiveness to the biological surface can be maintained, the storage elastic modulus can be lowered, and the viscosity can be improved. Since the elasticity can be increased, the noise generated during use can be suppressed. Moreover, the adhesive electrode 20 can suppress water absorption from the outside and suppress swelling.

The thickness of the adhesive electrode 20 is preferably 10 μm to 100 μm, more preferably 15 μm to 90 μm, even more preferably 20 μm to 80 μm. When the thickness of the adhesive electrode 20 is within the above preferable range, the adhesive electrode 20 can be provided with sufficient strength, flexibility, and conductive stability during deformation.

The thickness of the adhesive electrode 20 refers to the length in the direction perpendicular to the surface of the adhesive electrode 20. The thickness of the adhesive electrode 20 is, for example, the thickness measured at an arbitrary location in the cross section of the adhesive electrode 20, and when the thickness is measured at multiple locations at arbitrary locations, the thickness at these measurement locations. An average value may be used.

(Sensor part)
As shown in FIG. 3, the sensor section 30 has a flexible substrate 31, a sensor main body 32, and

connection sections

33A and 33B connected to the sensor main body 32. As shown in FIG.

The flexible board 31 is a resin board on which various parts for acquiring biometric information are mounted, and the flexible board 31 is provided with a sensor body 32 and connecting

portions

33A and 33B.

As shown in FIG. 2, the sensor main body 32 has a component mounting section 321 as a control section and a battery mounting section 322, and acquires biological information.

The component mounting unit 321 includes a CPU and an integrated circuit that process biological signals obtained from a living body and generate biological signal data, a switch that activates the biological sensor 1, a flash memory that stores biological signals, a light emitting element, and the like, and a flexible substrate 31. It has various parts mounted on the body and acquires biometric information. Note that an example of a circuit using various components is omitted. The component mounting portion 321 operates by power supplied from the battery 34 mounted on the battery mounting portion 322 .

The component mounting unit 321 transmits by wire or wirelessly to an external device such as an operation confirmation device for confirming the initial operation and a reading device for reading biometric information from the biosensor 1 .

The battery mounting section 322 is arranged between the connection section 33A and the component mounting section 321, and supplies electric power to the integrated circuit or the like mounted on the component mounting section 321. The battery 34 is attached to the battery attachment portion 322 as shown in FIG.

The

connection portions

33A and 33B are provided on the

wire

331A and 331B respectively connected to the sensor body 32 in the longitudinal direction (Y-axis direction) of the sensor body 32, and on the tip side of the

wire

331A and 331B, and are connected to the adhesive electrode 20. It has

terminal portions

332A and 332B that are connected.

One ends of the

wirings

331A and 331B are connected to the adhesive electrodes 20, respectively, as shown in FIG. As shown in FIG. 3, the other end of the wiring 331A is connected to a switch or the like mounted on the component mounting portion 321 along the outer periphery of the sensor main body 32. As shown in FIG. The other end of the wiring 331B is connected to a switch or the like mounted on the component mounting portion 321 . The

wirings

331A and 331B may be formed on either wiring layer on the front surface side or the rear surface side of the flexible substrate 31 .

The

terminal portions

332A and 332B have one end connected to the

wires

331A and 331B, and the upper surface of the other end is sandwiched between the first layer member 10 and the second layer member 40 while being in contact with the adhesive electrode 20. are placed in

A known battery can be used for the battery 34 . As the battery 34, for example, a coin type battery such as CR2025 can be used.

[Second layer member]
As shown in FIG. 3, the second layer member 40 is provided on the sticking surface side of the adhesive electrode 20 and the sensor section 30, and serves as a supporting substrate on which the sensor section 30 is installed, as well as a part of the sticking surface with the skin 2. to form As shown in FIGS. 1 and 2, the outer shape of both sides of the second layer member 40 in the width direction (X-axis direction) is substantially the same as the outer shape of both sides of the first layer member 10 in the width direction (X-axis direction). may be the same. The length (Y-axis direction) of the second layer member 40 is shorter than the length (Y-axis direction) of the cover member 11 and the upper sheet 12 . As shown in FIG. 3, both ends of the second layer member 40 in the longitudinal direction are positions where the

wires

331A and 331B of the sensor section 30 are sandwiched between the second layer member 40 and the upper sheet 12, and are adhesive electrodes. 20 and a part of it overlaps.

The second layer member 40 has a second base material 41 , a lower adhesive layer 42 provided on the upper surface of the second base material 41 , and a first adhesive layer 43 provided on the lower surface of the second base material 41 . The second base material 41, the lower adhesive layer 42, and the first adhesive layer 43 may be formed in the same shape in plan view. The first adhesive layer 43 of the second layer member 40 and the adhesive electrode 20 form a sticking surface to the skin 2 . Depending on the area of the adhesive electrode 20 and the first adhesive layer 43 and the position of the attachment surface, the waterproofness and moisture permeability can be different, and the adhesiveness can be different. Depending on the area of the surface, the waterproofness and moisture permeability can be differentiated, and the adhesiveness can be differentiated.

(Second base material)
The second base material 41 can be formed using a flexible resin having suitable stretchability, flexibility and toughness. Examples of materials for forming the second base material 41 include polyester resins such as polyethylene terephthalate (PET), polybutylene terephthalate, polytrimethylene terephthalate, polyethylene naphthalate, and polybutylene naphthalate; Acrylic resins such as polyacrylic acid, polymethacrylic acid, polymethyl acrylate, polymethyl methacrylate (PMMA), polyethyl methacrylate, polybutyl acrylate; polyolefin resins such as polyethylene and polypropylene; polystyrene, imide-modified polystyrene , acrylonitrile-butadiene-styrene (ABS) resin, imide-modified ABS resin, styrene-acrylonitrile copolymer (SAN) resin, acrylonitrile-ethylene-propylene-diene-styrene (AES) resin, polystyrene-based resin; polyimide-based resin; polyurethane Thermoplastic resins such as silicone-based resins; polyvinyl chloride-based resins such as polyvinyl chloride and vinyl chloride-vinyl acetate copolymer resins can be used. Among these, polyolefin resins and PET are preferably used. These thermoplastic resins are waterproof (low moisture permeability), impermeable to moisture and water vapor. Therefore, by forming the second base material 41 using these thermoplastic resins, in a state in which the biosensor 1 is attached to the skin 2 of the living body, sweat or water vapor generated from the skin 2 is transferred to the second base material 41 . Intrusion into the flexible substrate 31 side of the sensor section 30 through the base material 41 can be suppressed.

The second base material 41 is preferably formed in a flat plate shape because the sensor part 30 is installed on the upper surface side thereof with the lower adhesive layer 42 interposed therebetween.

The thickness of the second base material 41 can be selected arbitrarily, and may be, for example, 1 μm to 300 μm.

(Adhesive layer for lower part)
As shown in FIG. 3, the lower adhesive layer 42 is provided on the upper surface of the second base material 41 on the cover member 11 side (+Z-axis direction), and the sensor section 30 is adhered thereto. Both longitudinal end sides of the lower adhesive layer 42 of the second layer member 40 are provided at positions facing the facing portions 20a of the adhesive electrodes 20 . As a result, the opposing portion 20a of the adhesive electrode 20 and the

terminal portions

332A and 332B can be sandwiched between the upper sheet 12 and the second layer member 40 while being pressed, and the adhesive electrode 20 and the

terminal portions

332A and 332B can be sandwiched between the upper sheet 12 and the second layer member 40. 332B. The lower adhesive layer 42 can be made of the same material as the first adhesive layer 43, which will be described later, so the details are omitted. Note that the lower adhesive layer 42 is not necessarily provided, and may be omitted.

(First adhesive layer)
As shown in FIG. 3, the first adhesive layer 43 is provided on the bottom surface of the second substrate 41 on the sticking side (−Z axis direction), and is a layer that comes into contact with the living body.

The first adhesive layer 43 preferably has pressure-sensitive adhesive properties. Since the first adhesive layer 43 has pressure-sensitive adhesive properties, the biosensor 1 can be easily attached to the skin 2 by pressing the biosensor 1 against the skin 2 of the living body.

The material for the first adhesive layer 43 is not particularly limited as long as it has pressure-sensitive adhesive properties, and examples thereof include materials having biocompatibility. Materials for forming the first adhesive layer 43 include acrylic pressure-sensitive adhesives, silicone pressure-sensitive adhesives, and the like. Acrylic pressure-sensitive adhesives are preferred.

The acrylic pressure-sensitive adhesive preferably contains an acrylic polymer as a main component. Acrylic polymers can function as pressure sensitive adhesive components. The acrylic polymer includes a (meth)acrylic acid ester such as isononyl acrylate and methoxyethyl acrylate as a main component, and a monomer component that optionally contains a monomer that can be copolymerized with a (meth)acrylic acid ester such as acrylic acid. can be used.

The acrylic pressure-sensitive adhesive preferably further contains a carboxylic acid ester. The carboxylic acid ester functions as a pressure-sensitive adhesive strength adjuster that reduces the pressure-sensitive adhesive strength of the acrylic polymer and adjusts the pressure-sensitive adhesive strength of the first adhesive layer 43 . A carboxylic acid ester compatible with an acrylic polymer can be used as the carboxylic acid ester. As the carboxylic acid ester, tri-fatty acid glyceryl or the like can be used.

The acrylic pressure-sensitive adhesive may contain a cross-linking agent if necessary. A cross-linking agent is a cross-linking component that cross-links the acrylic polymer. Examples of cross-linking agents include polyisocyanate compounds (polyfunctional isocyanate compounds), epoxy compounds, melamine compounds, peroxide compounds, urea compounds, metal alkoxide compounds, metal chelate compounds, metal salt compounds, carbodiimide compounds, oxazoline compounds, aziridine compounds, amines. compounds and the like. Among these, polyisocyanate compounds are preferred. These cross-linking agents may be used alone or in combination.

The first adhesive layer 43 preferably has excellent biocompatibility. For example, when the first adhesive layer 43 is subjected to a keratin peeling test, the keratin peeling area ratio is preferably 0% to 50%. If the exfoliation area ratio is within the range of 0% to 50%, even if the first adhesive layer 43 is adhered to the skin 2, the load on the skin 2 can be suppressed.

The first adhesive layer 43 preferably has moisture permeability. Vapor or the like generated from the skin 2 to which the biosensor 1 is attached can escape to the upper sheet 12 side through the first adhesive layer 43 . In addition, since the upper sheet 12 has a cell structure as will be described later, water vapor can be released to the outside of the biosensor 1 through the first adhesive layer 43 . This can prevent sweat or water vapor from accumulating at the interface between the skin 2 on which the biosensor 1 is attached and the first adhesive layer 43 . As a result, moisture accumulated at the interface between the skin 2 and the first adhesive layer 43 weakens the adhesive force of the first adhesive layer 43 , thereby preventing the biosensor 1 from being peeled off from the skin.

The moisture permeability of the first adhesive layer 43 is preferably, for example, 300 (g/m ² ·day) to 10000 (g/m ² ·day). If the moisture permeability of the first adhesive layer 43 is within the above preferred range, even if the first adhesive layer 43 is adhered to the skin 2 , the perspiration generated from the skin 2 will be appropriately removed from the first adhesive layer 43 to the outside. , the burden on the skin 2 can be reduced.

The thickness of the first adhesive layer 43 can be selected arbitrarily, and is preferably 10 μm to 300 μm. If the thickness of the first adhesive layer 43 is 10 μm to 300 μm, the thickness of the biosensor 1 can be reduced.

As shown in FIGS. 1 and 2, the biosensor 1 protects the adhesive electrodes 20 and the second layer member 40 on the surfaces of the adhesive electrodes 20 and the second base material 41 that are attached to the living body when not in use. Therefore, it is preferable to attach the release liner 50 until use. At the time of use, the release liner 50 is peeled off from the adhesive electrode 20 and the second layer member 40 and the sticking surface of the biosensor 1 is stuck to the skin 2 . By attaching the release liner 50 to the attachment surface, the adhesive force of the adhesive electrode 20 and the second layer member 40 can be maintained even when the biosensor 1 is stored for a long period of time. Therefore, by peeling off the release liner 50 from the second layer member 40 and the adhesive electrode 20 at the time of use, the adhesive surface can be reliably attached to the skin 2 for use.

The manufacturing method of the biosensor 1 is not particularly limited, and can be manufactured using any suitable method. An example of a method for manufacturing the biosensor 1 will be described.

The first layer member 10, the adhesive electrode 20, the sensor section 30 and the second layer member 40 shown in FIGS. 1 and 2 are prepared. The first layer member 10, the adhesive electrode 20, the sensor section 30, and the second layer member 40 are not particularly limited as long as they can be manufactured by any method, and can be manufactured using any appropriate manufacturing method.

After preparing the first layer member 10, the adhesive electrode 20, the sensor section 30 and the second layer member 40, which constitute the biosensor 1 shown in FIG. . Thereafter, the first layer member 10, the adhesive electrode 20, the sensor section 30, and the second layer member 40 are laminated in this order from the first layer member 10 side toward the second layer member 40 side. Thereby, the biosensor 1 shown in FIG. 1 is obtained.

FIG. 4 is an explanatory diagram showing a state in which the biosensor 1 of FIG. 1 is attached to the chest of the subject P. FIG. As shown in FIG. 4, for example, the biosensor 1 is aligned in the longitudinal direction (Y-axis direction) with the sternum of the subject P, with one adhesive electrode 20 on the upper side and the other adhesive electrode 20 on the lower side. is affixed to the subject P's skin. The biosensor 1 is attached to the skin of the subject P by the first adhesive layer 43 of FIG. A biological signal such as an electrocardiogram signal is acquired by the sex electrodes 20 . The biosensor 1 stores the acquired biosignal data in a non-volatile memory such as a flash memory mounted on the component mounting section 321 .

As described above, the biosensor 1 includes the first layer member 10 , the adhesive electrode 20 and the second layer member 40 . forming Since the adhesive electrode 20 has adhesiveness, even if an adhesive layer or the like for bonding the adhesive electrode 20 is not provided to the first layer member 10 and the second layer member 40, The upper surface of the second layer member 40 can be adhered. Therefore, the thickness of the biosensor 1 can be reduced. In addition, since the adhesive electrode 20 can adhere to the skin 2, the adhesion to the skin 2 can be maintained. Therefore, the biosensor 1 can be made smaller and the contact impedance with the surface of the skin 2 can be reduced.

Further, in the biosensor 1, as described above, since the adhesive electrode 20 has adhesiveness, it is necessary to provide an adhesive layer or the like for bonding the adhesive electrode 20 to the first layer member 10 and the second layer member 40. can be made smaller. Therefore, the biosensor 1 can reduce manufacturing costs.

Furthermore, in the biosensor 1 , since the adhesive electrode 20 has adhesiveness as described above, the adhesive electrode 20 can be attached to the upper surface of the second layer member 40 . resistance can be reduced. Therefore, the biosensor 1 can more stably detect the biosignal acquired from the skin 2 .

The biosensor 1 can be provided with the adhesive electrodes 20 up to both ends of the first base material 121 in plan view of the biosensor 1 . Since the adhesive electrode 20 has adhesiveness as described above, it is not necessary to provide a region around the tip of the first layer member 10 for holding the adhesive electrode 20 to the first layer member 10 . Therefore, in the biosensor 1, the adhesive electrodes 20 can be provided to both ends of the first base material 121, so that the installation area of the adhesive electrodes 20 provided on the lower surface of the first layer member 10 can be increased. Therefore, the biosensor 1 can reliably acquire the biosignal.

The biosensor 1 can have a first adhesive layer 43 on the surface of the second layer member 40 opposite to the first layer member 10 side. Thereby, even if the surface of the skin 2 changes due to body movement or the like, the adhesive electrode 20 can adhere to the skin 2 more stably. Therefore, biosensor 1 can further reduce the negotiation impedance with the surface of skin 2 .

In the biosensor 1, the adhesive electrode 20 contains a conductive polymer, a binder resin, and a moisturizing agent, and the binder resin can be composed of a water-based emulsion adhesive. As a result, the adhesive electrode 20 can reduce resistance, increase viscoelasticity, and suppress swelling due to water absorption. Therefore, since the adhesive electrode 20 can improve water resistance, it can exhibit electrical conductivity and adhesive force, and can improve flexibility and followability to the surface of the living body. Therefore, since the adhesive electrode 20 can maintain the adhesive force with respect to the skin 2, the biosensor 1 can reduce the contact impedance with the surface of the skin 2 more reliably.

The biosensor 1 can use an acrylic emulsion adhesive as the water-based emulsion adhesive for the adhesive electrodes 20 . As a result, the adhesive electrode 20 can reliably improve the water resistance, thereby suppressing a decrease in the adhesive force while maintaining the resistance, and reliably enhancing the followability to the surface of the living body. Therefore, since the viscoelasticity of the adhesive electrode 20 can be reliably kept low, the adhesive electrode 20 can have high adhesive strength and conformability to the surface of the living body. Therefore, the biosensor 1 can reliably reduce the contact impedance with the surface of the skin 2 .

The biosensor 1 uses, as the acrylic emulsion adhesive for the adhesive electrode 20, a monomer mixture containing a (meth)acrylic acid alkyl ester and a silane-based monomer copolymerizable with the (meth)acrylic acid alkyl ester. A silane-based emulsion adhesive containing a water-dispersible copolymer obtained by copolymerization and an organic liquid component compatible with the water-dispersible copolymer can be used. As a result, the viscoelasticity of the adhesive electrode 20 can be reliably kept low, so that the adhesive force can be increased, and the followability to the surface of the living body can be further improved. Therefore, the biosensor 1 can further reliably reduce the contact impedance with the surface of the skin 2 .

The biosensor 1 uses, as an acrylic emulsion adhesive for the adhesive electrode 20, one or more components selected from the group including a monomer mixture containing a (meth)acrylic acid alkyl ester and a monomer mixture containing a carboxyl group. Two-component or three-component acrylic emulsion adhesives can be used, including: Even in this case, since the viscoelasticity of the adhesive electrode 20 can be reliably suppressed to a low level, the adhesive force can be increased, and the followability to the biological surface can be further improved. Therefore, the biosensor 1 can further reliably reduce the contact impedance with the surface of the skin 2 .

In the biosensor 1, the thickness of the adhesive electrode 20 can be set to 10 μm to 100 μm. As a result, the adhesive electrode 20 can reliably exhibit electrical conductivity and adhesive force, and can reliably keep viscoelasticity low, thereby reliably increasing the adhesive force and further improving the followability to the biological surface. be able to. Therefore, the biosensor 1 can further reliably reduce the contact impedance with the surface of the skin 2 .

In the biosensor 1, the sensor section 30 can have

connection sections

33A and 33B. The connecting

portions

33A and 33B are provided so as to partially overlap the adhesive electrodes 20 between the first layer member 10 and the second layer member 40 and connect the adhesive electrodes 20 to the sensor main body 32 . As a result, the biosensor 1 can maintain contact with the skin 2 and reliably maintain connection with the sensor main body 32, so that biosignals can be stably measured.

In the biosensor 1, the first layer member 10 includes the cover member 11, the first base material 121, and the upper adhesive layer 122, and the upper adhesive layer 122 is attached to the second layer member 40 side of the first base material 121. can be provided. The first base material 121 has a through hole 121a at a position corresponding to the storage space S, and can have a porous structure. For this reason, since the first layer member 10 has the first base material 121, even if sweat or water vapor that has entered the first base material 121 can be easily released to the outside, the first base material 121 and It is possible to reduce the occurrence of detachment from the adhesive electrode 20 or the upper adhesive layer 122 . Therefore, the biosensor 1 can more stably maintain the contact of the adhesive electrode 20 with the skin 2 and the connection with the sensor main body 32, so that the biosignal can be stably measured. Damage to the biosensor 1 can be reduced.

As described above, the biosensor 1 can stably measure biometric information from the skin 2 during use for a long period of time. can be used. The biosensor 1 is attached to the skin of a living body, for example, and can be suitably used for healthcare wearable devices that require high electrocardiogram detection sensitivity and a high effect of suppressing noise generated in the electrocardiogram.

Although the embodiment has been described as above, the above embodiment is presented as an example, and the present invention is not limited by the above embodiment. The above embodiments can be implemented in various other forms, and various combinations, omissions, replacements, changes, etc. can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the scope of the invention described in the claims and equivalents thereof.

In addition, the aspect of embodiment of this invention is as follows, for example.
<1> a sensor body that acquires biological information;
a sticky electrode connected to the sensor body;
a first layer member having the electrode provided on its lower surface;
a second layer member that is attached so as to expose the electrodes on the lower surface of the first layer member and cover the sensor body;
with
A biosensor, wherein a surface to be adhered to a living body is formed by the electrodes and the second layer member.
<2> The biosensor according to <1>, wherein the electrodes extend to both ends of the first layer member in plan view of the biosensor.
<3> The biosensor according to <1> or <2>, wherein the second layer member has a first adhesive layer on a surface opposite to the first layer member.
<4> The biosensor according to any one of <1> to <3>, wherein the electrode includes a conductive polymer, a binder resin made of an aqueous emulsion adhesive, and a moisturizing agent.
<5> The biosensor according to <4>, wherein the aqueous emulsion adhesive is an acrylic emulsion adhesive.
<6> The acrylic emulsion pressure-sensitive adhesive is water obtained by copolymerizing a monomer mixture containing a (meth)acrylic acid alkyl ester with a silane-based monomer copolymerizable with the (meth)acrylic acid alkyl ester. The biosensor according to <5>, which contains a dispersed copolymer and an organic liquid component compatible with the water-dispersed copolymer.
<7> The biosensor according to <5>, wherein the acrylic emulsion adhesive contains a monomer mixture containing a (meth)acrylic acid alkyl ester and a carboxyl group-containing monomer.
<8> The biosensor according to any one of <1> to <7>, wherein the electrode has a thickness of 10 μm to 100 μm.
<9><1> to <8> having a connecting portion provided between the first layer member and the second layer member so as to overlap with a part of the electrode and connecting the electrode to the sensor main body; The biosensor according to any one of 1.
<10> The first layer member is
a cover member having a storage space in which the sensor main body is stored;
a first base material having a porous structure and having a through hole at a position corresponding to the storage space;
an upper adhesive layer for attaching the cover member and the first base material;
with
The biosensor according to any one of <1> to <9>, wherein the electrode is provided on the second layer member side of the first base material.

This application claims priority based on Japanese Patent Application No. 2021-205940 filed with the Japan Patent Office on December 20, 2021, and incorporates all the contents described in the above application.

Reference Signs List 1 biosensor 2 skin 10 first layer member 11 cover member 12

upper sheet

12a, 121a, 122a through hole through

hole

20, 20A, 20B adhesive electrode 20a opposing portion 20b exposed portion 30 sensor section 31 flexible substrate 32 sensor main body

33A connection Part

33A, 33B Connection Part 34 Battery 40 Second Layer Member 41 Second Base Material 42 Lower Adhesive Layer 43 First Adhesive Layer 111 Protruding Part 111a

Recess

112A, 112B Flat Part 121 First Base Material 122 Upper Adhesive Layer 321 Parts Mounting portion 322

Battery mounting portion

331A,

331B Wiring

332A, 332B Terminal portion

Claims

a sensor body that acquires biological information;
a sticky electrode connected to the sensor body;
a first layer member having the electrode provided on its lower surface;
a second layer member that is attached so as to expose the electrodes on the lower surface of the first layer member and cover the sensor body;
with
A biosensor, wherein a surface to be adhered to a living body is formed by the electrodes and the second layer member.
The biosensor according to claim 1, wherein the electrodes extend to both ends of the first layer member in plan view of the biosensor.
The biosensor according to claim 1, wherein the second layer member has a first adhesive layer on the side opposite to the first layer member side.
The biosensor according to claim 1, wherein the electrode contains a conductive polymer, a binder resin made of a water-based emulsion adhesive, and a moisturizing agent.
The biosensor according to claim 4, wherein the aqueous emulsion adhesive is an acrylic emulsion adhesive.
The acrylic emulsion adhesive is a water-dispersible copolymer obtained by copolymerizing a monomer mixture containing an (meth)acrylic acid alkyl ester with a silane-based monomer copolymerizable with the (meth)acrylic acid alkyl ester. 6. The biosensor according to claim 5, comprising a polymer and an organic liquid component compatible with the water-dispersible copolymer.
The biosensor according to claim 5, wherein the acrylic emulsion adhesive contains a monomer mixture containing a (meth)acrylic acid alkyl ester and a carboxyl group-containing monomer.
The biosensor according to claim 1, wherein the electrode has a thickness of 10 μm to 100 μm.
The biosensor according to claim 1, further comprising a connecting portion provided between the first layer member and the second layer member so as to partially overlap the electrode and connecting the electrode to the sensor main body.
The first layer member is
a cover member having a storage space in which the sensor main body is stored;
a first base material having a porous structure and having a through hole at a position corresponding to the storage space;
an upper adhesive layer for attaching the cover member and the first base material;
with
The biosensor according to claim 1, wherein the electrode is provided on the second layer member side of the first base material.