Adhesive electrode for acquiring biological signal and biological sensor

Abstract

The adhesive electrode for biosignal acquisition according to the present invention is an adhesive electrode for biosignal acquisition comprising a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive, wherein the content of the nitrogen-containing additive is 0.01-3.0 wt% relative to the total amount of the adhesive electrode for biosignal acquisition.

Description

Technical Field

[0001] The present invention relates to an adhesive electrode and a biosensor for acquiring biological signals. Background Art

[0002] Wearable biosensors that acquire biometric information such as electrocardiogram waveforms, pulse waves, brain waves, and myoelectricity are used in medical institutions such as hospitals and clinics, nursing facilities, and at home. The biosensor has an adhesive electrode (bioelectrode) for acquiring biometric signal that contacts the subject's biometric information. When measuring the biometric information, the biosensor is attached to the subject's skin, and the bioelectrode acquires an electrical signal related to the biometric information, thereby measuring the biometric information.

[0003] As a biological electrode for such a biological sensor, for example, there is disclosed an adhesive layer comprising a conductive organic polymer compound and an adhesive material, in which PEDOT:PSS is used as the conductive organic polymer compound, an aqueous emulsion is used as the adhesive material, and the adhesive sheet is adhered to the skin surface of a wiring substrate (for example, refer to patent document 1).

[0004] Prior art literature

[0005] Patent Literature

[0006] Patent Document 1: Japanese Patent Application Publication No. 2020-147659 Summary of the invention

[0007] Problems to be solved by the invention

[0008] However, the water-based emulsion used in the adhesive material has the property of absorbing water easily. Therefore, the adhesive sheet of Patent Document 1 has the problem that when it is attached to the skin, it absorbs sweat and water present outside, and the adhesive strength is reduced and it is easy to peel off from the skin, and the biological signal cannot be stably measured with high sensitivity.

[0009] An object of one embodiment of the present invention is to provide an adhesive electrode for acquiring a biological signal that can stably perform measurement with high sensitivity even if the electrode absorbs moisture from the outside during use.

[0010] Methods for solving problems

[0011] One embodiment of the adhesive electrode for acquiring biological signals according to the present invention is an adhesive electrode for acquiring biological signals comprising a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive.

[0012] The content of the nitrogen-containing additive is 0.01 wt % to 3.0 wt % based on the total amount of the biosignal acquiring adhesive electrode.

[0013] Effects of the Invention

[0014] One aspect of the adhesive electrode for acquiring biological signals according to the present invention can stably perform measurement with high sensitivity even if the electrode absorbs moisture from the outside during use. BRIEF DESCRIPTION OF THE DRAWINGS

[0015] Figure 1 It is a graph showing the relationship between the water absorption rate and the contact impedance of the electrode sheet of each example and comparative example.

[0016] Figure 2 It is a graph showing the relationship between the water absorption rate and the adhesive force of the electrode sheet of each Example and Comparative Example. DETAILED DESCRIPTION

[0017] Hereinafter, the embodiments of the present invention will be described in detail. In addition, in the present specification, "to" indicating a numerical range means that the numerical values ​​described before and after it are included as the lower limit and the upper limit unless otherwise specified.

[0018] <Adhesive electrodes for acquiring biological signals>

[0019] The adhesive electrode for obtaining biological signals according to the present embodiment is described. In addition, the biological body refers to the human body (human), as well as animals such as cows, horses, pigs, chickens, dogs and cats. The biological sensor according to the present embodiment can be used for biological bodies, and can be used as a human body. In the present embodiment, as an example, the case where the biological body is a human is described.

[0020] The biometric signal acquisition adhesive electrode involved in this embodiment is a biometric electrode that is attached to a part of a living body (e.g., skin, scalp, or forehead) to detect biometric information. In this embodiment, the case where the biometric signal acquisition adhesive electrode is attached to the skin of a person to acquire an electrical signal (biometric signal) related to the person's biometric information is described. In addition, the biometric signal is, for example, an electrical signal representing an electrocardiogram waveform, an electroencephalogram, a pulse, etc.

[0021] The biometric signal acquisition adhesive electrode according to the present embodiment has a sheet-like shape, and when viewed from above, one side (one end side) of the biometric signal acquisition adhesive electrode in the length direction is formed in a substantially rectangular shape, and the other side (the other end side) in the length direction is formed in a substantially arc shape. The biometric signal acquisition adhesive electrode is, for example, attached to the skin as an example of a living body so that it contacts the skin, thereby measuring the potential difference (polarization voltage) between the skin and the biometric signal acquisition adhesive electrode, and can be used to detect an electrical signal (biometric signal) related to the biometric information of the subject.

[0022] In addition, the bio-signal acquisition adhesive electrode may have other shapes besides a sheet shape, such as a rod shape. In addition, the shape of the bio-signal acquisition adhesive electrode when viewed from above is not limited to the above-mentioned shape, and may be designed to be any appropriate shape according to the purpose, and may be formed into any shape such as a roughly rectangular shape, a roughly polygonal shape, a roughly circular shape, or a roughly elliptical shape.

[0023] The thickness of the adhesive electrode for acquiring biological signals involved in this embodiment can be made into any appropriate thickness within the range that can ensure strength, flexibility, low resistance and conductivity according to its use, size, etc. In addition, the thickness of the adhesive electrode for acquiring biological signals refers to the length in the direction perpendicular to the surface of the adhesive electrode for acquiring biological signals. The thickness of the adhesive electrode for acquiring biological signals is, for example, the thickness when measuring an arbitrary place in the cross section of the adhesive electrode for acquiring biological signals. When measuring multiple places at an arbitrary place, the average value of the thicknesses at these measured places can be used.

[0024] The biological signal acquisition adhesive electrode according to the present embodiment is an adhesive electrode (adhesive electrode) and includes a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive, and may include any components such as a moisturizer and additives.

[0025] The inventors of the present application have focused on the fact that when an adhesive electrode for acquiring biological signals comprising a conductive polymer and an aqueous emulsion adhesive is used, when the adhesive electrode for acquiring biological signals absorbs moisture such as sweat, the aqueous emulsion adhesive absorbs water, thereby reducing the adhesive force of the adhesive electrode for acquiring biological signals. The inventors of the present application have found that if the adhesive electrode for acquiring biological signals comprising a conductive polymer and an aqueous emulsion adhesive contains a nitrogen-containing additive, the nitrogen-containing additive quickly absorbs moisture existing around the adhesive electrode for acquiring biological signals such as sweat at the interface between the adhesive electrode for acquiring biological signals and the skin, thereby suppressing the reduction in the adhesiveness of the adhesive electrode for acquiring biological signals. The inventors of the present application have found that by including a predetermined amount of nitrogen-containing additives in the adhesive electrode for acquiring biological signals, water resistance is improved, and while maintaining an adhesive force to the extent that it can be attached to the skin, the contact impedance to the skin is increased, and an adhesive electrode for acquiring biological signals that can stably perform measurements with high sensitivity is obtained.

[0026] As the conductive polymer contained in the adhesive electrode for obtaining biological signals involved in the present embodiment, for example, polythiophene-based conductive polymers, polyaniline-based conductive polymers, polypyrrole-based conductive polymers, polyacetylene-based conductive polymers, polyphenylene-based conductive polymers and their derivatives, and their complexes, etc. can be used. They can be used alone or in combination of two or more. Among these, it is preferred to use a complex in which polythiophene is doped with polyaniline as a dopant. Among the complexes of polythiophene and polyaniline, from the perspective of further reducing the contact impedance with the organism and having high conductivity, it is more preferred to use PEDOT / PSS in which poly-3,4-ethylenedioxythiophene (PEDOT) is doped with polystyrene sulfonic acid (poly-4-styrene sulfonate; PSS).

[0027] The aqueous emulsion adhesive contained in the adhesive electrode for acquiring biological signals according to the present embodiment is used as a binder resin of the adhesive electrode for acquiring biological signals. The aqueous emulsion adhesive has the function of improving the adhesiveness and softness of the adhesive electrode for acquiring biological signals. Therefore, the aqueous emulsion adhesive is contained in the adhesive electrode for acquiring biological signals, so that the adhesive electrode for acquiring biological signals can be made low in elasticity and improve the ability to follow the unevenness of the skin surface.

[0028] As the water-based emulsion adhesive, an acrylic emulsion adhesive is preferably used.

[0029] The acrylic emulsion adhesive is preferably a silane emulsion adhesive containing a water-dispersible copolymer and an organic liquid component compatible with the water-dispersible copolymer.

[0030] The water-dispersible copolymer is a polymer obtained by copolymerizing a silane-based monomer copolymerizable with an alkyl (meth)acrylate in a monomer mixture containing an alkyl (meth)acrylate.

[0031] The monomer mixture containing an alkyl (meth)acrylate refers to a monomer mixture containing an alkyl (meth)acrylate as a main component, preferably containing 50 wt % to 100 wt %.

[0032] As the alkyl (meth)acrylate, a linear or branched alkyl ester having an alkyl group with 1 to 15 carbon atoms, preferably 1 to 9 carbon atoms, is used. Specifically, for example, alkyl (meth)acrylate having a linear or branched alkyl group such as 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, decyl (meth)acrylate, undecyl (meth)acrylate, tridecyl (meth)acrylate, etc., can be mentioned. These can be used alone or in combination of two or more.

[0033] The monomer mixture containing the alkyl (meth)acrylate may contain a carboxyl group-containing monomer copolymerizable with the alkyl (meth)acrylate.

[0034] 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 not particularly limited as long as it is copolymerizable with the (meth)acrylic acid alkyl ester, and examples thereof include (meth)acrylic acid, itaconic acid, maleic acid, maleic anhydride, 2-methacryloyloxyethylsuccinic acid, etc. Acrylic acid is particularly preferred.

[0035] The carboxyl group-containing monomer is preferably contained in an amount of 0.1 wt % to 10 wt % based on 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 obtained adhesiveness.

[0036] As the silane monomers copolymerizable with (meth) alkyl acrylate, it is a polymerizable compound having a silicon atom. If it can be copolymerized with (meth) alkyl acrylate, it is not particularly limited. From the perspective of excellent copolymerizability with (meth) alkyl acrylate, it is preferably a silane compound having a (meth) acryloyl group such as a (meth) acryloyloxyalkylsilane derivative. As the silane monomers, for example, 3-(meth) acryloyloxypropyl trimethoxysilane, 3-(meth) acryloyloxypropyl triethoxysilane, 3-(meth) acryloyloxypropyl methyl dimethoxysilane, 3-(meth) acryloyloxypropyl methyl diethoxysilane, etc. can be cited. These silane monomers can be used alone or in combination of two or more.

[0037] In addition, as silane monomers other than the above, for example, vinyltrimethoxysilane, vinyltriethoxysilane, 4-vinylbutyltrimethoxysilane, 4-vinylbutyltriethoxysilane, 8-vinyloctyltrimethoxysilane, 8-vinyloctyltriethoxysilane, 10-methacryloyloxydecyltrimethoxysilane, 10-acryloyloxydecyltrimethoxysilane, 10-methacryloyloxydecyltriethoxysilane, 10-acryloyloxydecyltriethoxysilane, etc. can also be used.

[0038] The silane-based monomer is preferably copolymerized in an amount of 0.005 wt % to 2 wt % based on 100 wt % of the monomer mixture containing the alkyl (meth)acrylate.

[0039] The silane monomer is copolymerized with a monomer mixture containing an alkyl (meth)acrylate, so that the silane compound as a crosslinking point is uniformly present in the molecules of the resulting copolymer. Therefore, the water-based emulsion adhesive, whether or not it is a water-dispersible type, has excellent cohesive force because the inside and outside of the particles of the water-based emulsion adhesive are uniformly crosslinked, and has low skin irritation due to the addition of an organic liquid component, and also has excellent fixation and sweat-resistant fixation.

[0040] The water-dispersible copolymer can be copolymerized with monomers other than the above-mentioned silane monomers and carboxyl-containing monomers that can be copolymerized with alkyl (meth)acrylates as needed. The monomers other than the silane monomers and carboxyl-containing monomers that can be copolymerized with alkyl (meth)acrylates can be used for the purpose of adjusting the cohesive force of the adhesive electrode for obtaining biological signals when the aqueous emulsion adhesive is formed into a sheet, etc., and improving the compatibility with organic liquid components, etc. The amount used can replace a part of the content of the alkyl (meth)acrylate and can be arbitrarily set according to the purpose.

[0041] Examples of the monomer copolymerizable with the alkyl (meth)acrylate other than the silane monomer and the carboxyl group-containing monomer include sulfonyl group-containing monomers such as styrenesulfonic acid, allylsulfonic acid, sulfopropyl (meth)acrylate, (meth)acryloyloxynaphthalenesulfonic acid, and acrylamidomethylpropanesulfonic acid; hydroxyl group-containing monomers such as hydroxyethyl (meth)acrylate and hydroxypropyl (meth)acrylate; amide group-containing monomers such as (meth)acrylamide, dimethyl (meth)acrylamide, N-butylacrylamide, N-methylol (meth)acrylamide, and N-methylolpropane (meth)acrylamide; alkylaminoalkyl (meth)acrylates such as aminoethyl (meth)acrylate, dimethylaminoethyl (meth)acrylate, and tert-butylaminoethyl (meth)acrylate; and (meth)acrylates containing an alkoxy group (or an ether bond in the side chain) such as methoxyethyl (meth)acrylate, ethoxyethyl (meth)acrylate, ...

[0042] The water-dispersible polymer can be prepared as a water dispersion of an alkyl (meth)acrylate copolymer by subjecting a monomer mixture containing an alkyl (meth)acrylate and a mixture of a silane-based monomer to conventional emulsion polymerization.

[0043] As the polymerization method, general batch polymerization, continuous drop polymerization, divided drop polymerization and the like can be adopted, and the polymerization temperature is, for example, 20°C to 100°C.

[0044] The polymerization initiator used for the polymerization is not particularly limited, and a general component used as a polymerization initiator can be used.

[0045] In order to adjust the degree of polymerization during polymerization, a chain transfer agent may be used. The chain transfer agent is not particularly limited, and a general component used as a chain transfer agent can be used.

[0046] In addition to the above-mentioned method, the water-dispersible copolymer can be prepared by obtaining a copolymer of a monomer mixture containing a (meth)acrylate and a silane-based monomer by a method other than emulsion polymerization and then dispersing the copolymer in water with an emulsifier.

[0047] The organic liquid component contained in the acrylic emulsion adhesive is blended with the water-dispersible copolymer to maintain good adhesion to the skin surface while reducing keratin damage and pain during peeling from the skin surface.

[0048] The organic liquid component is preferably liquid at room temperature and has good compatibility with the water-dispersible copolymer. In addition, "compatible" means that the organic liquid component is uniformly dissolved and taken up in the water-dispersible copolymer and cannot be visually observed to be separated.

[0049] Examples of the organic liquid component include esters of monobasic or polybasic acids having 8 to 18 carbon atoms and branched alcohols having 14 to 18 carbon atoms, and esters of unsaturated fatty acids or branched acids having 14 to 18 carbon atoms and alcohols having a valence of less than 4.

[0050] Examples of esters of a monobasic acid or polybasic acid having 8 to 18 carbon atoms and a branched alcohol having 14 to 18 carbon atoms include isostearyl laurate, isocetyl myristate, octyldodecyl myristate, isostearyl palmitate, isocetyl stearate, octyldodecyl oleate, diisostearyl adipate, diisocetyl sebacate, trioleyl trimellitate, and triisocetyl trimellitate.

[0051] Examples of the unsaturated fatty acid or branched acid having 14 to 18 carbon atoms include myristic acid, oleic acid, linoleic acid, linolenic acid, isopalmitic acid, and isostearic acid.

[0052] Examples of the tetravalent or lower alcohol include ethylene glycol, propylene glycol, glycerin, trimethylolpropane, pentaerythritol, and sorbitan.

[0053] The content of the organic liquid component can be appropriately and arbitrarily set according to the types of the water-dispersible copolymer and the organic liquid component, and can be, for example, 20 wt % to 80 wt % based on 100 wt % of the water-dispersible copolymer.

[0054] When the acrylic emulsion adhesive is a silane emulsion adhesive, specifically, a silane emulsion adhesive containing 2-ethylhexyl acrylate, methyl methacrylate, acrylic acid, and 3-methacryloxypropyltrimethoxysilane can be used as the acrylic emulsion adhesive.

[0055] In addition, the acrylic emulsion adhesive can be a two-component or three-component acrylic emulsion adhesive containing a monomer mixture containing an alkyl (meth)acrylate and a monomer containing a carboxyl group. These can contain a solvent and other components in appropriate predetermined amounts within a range in which the performance can be exerted.

[0056] The monomer mixture containing an alkyl (meth)acrylate contained in the two-component or three-component acrylic emulsion adhesive is the same as the monomer mixture containing an alkyl (meth)acrylate contained in the above-mentioned silane emulsion adhesive, and therefore the details are omitted.

[0057] The carboxyl group-containing monomer is preferably a carboxyl group-containing monomer copolymerizable with an alkyl (meth)acrylate. The carboxyl group-containing monomer copolymerizable with an alkyl (meth)acrylate is the same as the carboxyl group-containing monomer contained in the monomer mixture containing an alkyl (meth)acrylate, and thus the details are omitted.

[0058] As the two-component acrylic emulsion adhesive, specifically, an adhesive containing 2-ethylhexyl acrylate as a monomer mixture containing an alkyl (meth)acrylate, and acrylic acid as a monomer mixture containing a carboxyl group can be used.

[0059] As the three-component acrylic emulsion adhesive, specifically, an adhesive containing 2-ethylhexyl acrylate and methyl methacrylate as a monomer mixture containing an alkyl (meth)acrylate, and acrylic acid as a monomer mixture containing a carboxyl group can be used.

[0060] The average particle size of the aqueous emulsion adhesive is preferably 100 nm to 1.0 μm, more preferably 100 nm to 500 nm, and even more preferably 100 nm to 300 nm. When the average particle size is within the above preferred range, adhesive force and water resistance can be imparted to the biosignal acquisition adhesive electrode.

[0061] The shape of the aqueous emulsion adhesive is not particularly limited, and may be, for example, spherical, ellipsoidal, spindle-shaped, crushed, plate-shaped, columnar, or the like.

[0062] The average particle size refers to the volume average particle size using the effective diameter. The average particle size is, for example, the particle size distribution curve obtained by measuring the particle size distribution of the emulsion adhesive or the acrylic emulsion adhesive by laser diffraction-scattering method or dynamic light scattering method, and the cumulative amount is accumulated from the side with smaller particles, and the particle size (median particle size) when it occupies 50% on a volume basis.

[0063] The content of the aqueous emulsion adhesive is preferably 35wt% to 90wt% relative to 100wt% of the adhesive electrode for acquiring biological signals, more preferably 40wt% to 85wt%, and further preferably 50wt% to 80wt%. If the content of the aqueous emulsion adhesive is within the above-mentioned preferred range, it is possible to impart adhesion and softness to the adhesive electrode for acquiring biological signals while suppressing the reduction of conductivity.

[0064] The nitrogen-containing additive included in the adhesive electrode for acquiring biological signals according to the present embodiment has the property of invading the adhesive electrode for acquiring biological signals or absorbing the moisture that the surface of the adhesive electrode for acquiring biological signals 1 contacts. Even if the aqueous emulsion adhesive included in the adhesive electrode for acquiring biological signals has water absorption, the nitrogen-containing additive can invading the adhesive electrode for acquiring biological signals or the moisture that the adhesive electrode for acquiring biological signals contacts from the outside, thereby maintaining the adhesiveness of the aqueous emulsion adhesive. In addition, in the case of a conductive polymer such as PEDOT-PSS, PSS also has water absorption and has the property of easily absorbing moisture. By absorbing moisture through the nitrogen-containing additive, PSS can maintain the function as a dopant and dispersant of PEDOT, so that the adhesive electrode for acquiring biological signals can maintain conductivity in a high state.

[0065] The nitrogen-containing additive may include a nitrogen-containing compound containing a nitrogen atom, a nitrogen-containing resin (resin containing a nitrogen atom), and the like, and may be composed only of a nitrogen-containing compound or a nitrogen-containing resin.

[0066] As nitrogen-containing compounds, imidazole compounds, low molecular weight amines, polyvinyl pyrrolidone, polyethyleneimine, peptides, amino acids, melamine, etc. are used. Among these, imidazole compounds are preferred from the perspective of high water absorption and flexibility. They can be used alone or in combination of two or more.

[0067] The imidazole compound is an organic structure having an imidazole group. Examples of the imidazole compound include heterocyclic amines.

[0068] Examples of the heterocyclic amine include imidazole, 2-methylimidazole, 2-propylimidazole, 2-undecylimidazole, 2-phenylimidazole, N-methylimidazole, 1-(2-hydroxyethyl)imidazole, 2-ethyl-4-methylimidazole, 1,2-dimethylimidazole, 1-benzyl-2-methylimidazole, 1-benzyl-2-phenylimidazole, 1-cyanoethyl-2-methylimidazole, 1-cyanoethyl-2-ethyl-4-methylimidazole, 2-phenyl-4,5-dihydroxymethylimidazole, 1-acetylimidazole, 4,5-imidazoledicarboxylic acid, 4,5-imidazoledicarboxylic acid dimethyl, benzimidazole, 2-aminobenzimidazole, 2-aminobenzimidazole-2-sulfonic acid, 2-amino-1-methylbenzimidazole, 2-hydroxybenzimidazole, and 2-(2-pyridyl)benzimidazole. Among these, imidazole is preferred. The heterocyclic amines may be used alone or in combination of two or more.

[0069] In addition, the imidazole compound functions as a neutralizer in the region of pH 3.5 to 6.5 at the imidazole group, for example, and thus can neutralize the pH of the biosignal acquiring adhesive electrode.

[0070] As low molecular weight amines, for example, ethylenediamine, ethylamine, methylamine, dimethylamine, trimethylamine, triethylamine, triethanolamine, monoethanolamine, 2-dimethylaminoethanol, diethylamine, diethylaminoethanol, diisopropanolamine, aniline, benzylamine, pyridine, pyrazole compounds, etc. These may be used alone or in combination of two or more.

[0071] The nitrogen-containing resin is not particularly limited as long as it has water absorbency, and for example, urea-based resins and the like can be used.

[0072] The content of the nitrogen-containing additive is 0.01wt% to 3.0wt% relative to the total amount (100wt%) of the adhesive electrode for acquiring biological signals, preferably 0.1wt% to 2.5wt%, more preferably 0.3wt% to 2wt%, and further preferably 0.5wt% to 2.0wt%.

[0073] The nitrogen content in the nitrogen-containing additive is preferably 5 wt% to 45 wt%, more preferably 8 wt% to 40 wt%, and further preferably 9 wt% to 30 wt%, based on the total amount (100 wt%) of the nitrogen-containing additive.

[0074] When two nitrogen-containing additives are mixed and used, the mixing ratio of the nitrogen-containing additives is not particularly limited, and any appropriate ratio can be adopted according to the type of nitrogen-containing additives, for example, preferably 10:1 to 1:10, more preferably 5:1 to 1:5, and further preferably 3:1 to 1:3.

[0075] As described above, the biological signal acquiring adhesive electrode may contain a moisturizer, an additive, and the like as optional components.

[0076] The moisturizing agent has the function of improving the conductivity of the adhesive electrode for acquiring biological signals, and improving the adhesiveness and flexibility.

[0077] As the moisturizing agent, polyol compounds such as glycerol, ethylene glycol, propylene glycol, sorbitol, and polymers thereof, such as N-methylpyrrolidone (NMP), dimethylformaldehyde (DMF), N-N'-dimethylacetamide (DMAc), and aprotic compounds such as dimethyl sulfoxide (DMSO) can be cited. They can be used alone or in combination of two or more. Among these, glycerol is preferably used from the viewpoint of compatibility with other components.

[0078] The content of the moisturizer is preferably 2wt% to 60wt% relative to 100wt% of the adhesive electrode for acquiring biological signals, more preferably 3wt% to 50wt%, and further preferably 5wt% to 35wt%. If the content of the moisturizer is within the above-mentioned preferred range, the adhesive force of the adhesive electrode for acquiring biological signals can be increased, and while maintaining high adhesion to the surface of the skin, the storage elastic modulus can be reduced and the viscoelasticity can be increased, thereby suppressing the size of the noise generated during use. In addition, the adhesive electrode for acquiring biological signals can suppress water absorption from the outside and suppress swelling.

[0079] The additive has a neutralizing effect on the conductive polymer, neutralizing the conductive polymer while improving flexibility. In the case where the conductive polymer is, for example, PEDOT-PSS, the additive can form an organic salt when neutralized with PSS, which is a strong acid, and improves water absorption while playing an effect of making it insoluble in water.

[0080] Preferred examples of the additive include imidazole compounds, etc. The imidazole compound is the same as described above, and thus the details are omitted.

[0081] The content of the additive is preferably 0.5 wt% to 2.4 wt%, more preferably 0.7 wt% to 2.2 wt%, and further preferably 0.8 wt% to 2.0 wt%, based on 100 wt% of the biosignal acquiring adhesive electrode.

[0082] The method for producing the adhesive electrode for acquiring biological signals is not particularly limited. An example of the method for producing the adhesive electrode for acquiring biological signals is described below. For example, first, a conductive polymer and water are mixed to prepare a solution containing the conductive polymer (a step of preparing a solution containing the conductive polymer).

[0083] The mixing ratio of the conductive polymer and water, the mixing conditions such as mixing time, the temperature of the solution containing the conductive polymer, etc. are not particularly limited, and can be set to any appropriate size as long as the conductive polymer can be fully mixed with the solution containing the conductive polymer.

[0084] Next, a water-based emulsion adhesive, a moisturizer, and a nitrogen-containing additive are mixed with the solution containing the conductive polymer to prepare an adhesive composition aqueous solution (mixing step). The adhesive composition aqueous solution is used as an adhesive electrode forming composition.

[0085] There are no particular limitations on the mixing ratio of the solution containing the conductive polymer, the aqueous emulsion adhesive, the humectant and the nitrogen-containing additive, the mixing conditions such as the mixing time, and the temperature of the aqueous solution of the adhesive composition. If the aqueous emulsion adhesive, the humectant and the nitrogen-containing additive can be fully mixed in the solution containing the conductive polymer, the size can be set to any appropriate value.

[0086] Next, the adhesive composition aqueous solution is applied to the surface (coating surface) of the release substrate and then dried to evaporate the water contained in the adhesive composition aqueous solution (coating and drying process). The aqueous emulsion adhesive has a particle shape, so by applying the adhesive composition aqueous solution to the coating surface of the release substrate, the aqueous emulsion adhesives are bonded and fused to each other to form a coating film as a cured product of the adhesive electrode forming composition.

[0087] As the release substrate, a release liner or a core material can be used. As the release liner, a resin film such as polyethylene terephthalate (PET) film, polyethylene (PE) film, polypropylene (PP) film, polyamide (PA) film, polyimide (PI) film, or fluororesin film can be used. As the core material, a resin film such as PET film, PI film, a ceramic sheet, a metal film such as aluminum foil, a resin substrate reinforced with glass fiber, plastic nonwoven fiber, etc., a silicone substrate, a glass substrate, etc. can be used.

[0088] The method for applying the aqueous adhesive composition solution to the coating surface on the release substrate is not particularly limited as long as the aqueous adhesive composition solution can be applied to the release substrate, and a general coating method can be used.

[0089] As the coating method, it is possible to use a method utilizing roller coating, screen coating, gravure coating, spin coating, reverse coating, rod coating, blade coating, spray coating, air knife coating, dipping, dispensing, etc., a method utilizing a small amount of the adhesive composition aqueous solution to be suspended on the coating surface of the substrate and stretched using a blade, etc. By these coating methods, the adhesive composition aqueous solution is uniformly coated on the coating surface.

[0090] The drying conditions of the aqueous adhesive composition applied to the coating surface of the release substrate are not particularly limited as long as the aqueous adhesive composition applied to the release substrate can be dried, and general drying conditions can be used.

[0091] When drying, it can be dried at room temperature, and a drying machine can be used for heating. As the drying machine, a general drying machine such as a drying oven, a vacuum drying oven, an air circulation type drying oven, a hot air drying machine, a far infrared drying machine, a microwave decompression drying machine or a high frequency drying machine can be used. Using these drying machines, the adhesive composition aqueous solution coated on the coating surface of the substrate can be dried by a method of heating the inside of the drying machine to a high temperature, a method of heating the substrate, a method of blowing hot air into the adhesive composition aqueous solution, or a method of irradiating the adhesive composition aqueous solution with far infrared rays, microwaves, or high frequencies, etc.

[0092] The heating temperature and heating time when the adhesive composition aqueous solution is continuously heated using a dryer are the temperature and time that can evaporate the water contained in the adhesive composition aqueous solution. As the heating temperature, for example, it can be 100°C to 200°C. In the case where the conductive composition contains a crosslinking agent, if the heating temperature is in the range of 100°C to 200°C, the evaporation of the water contained in the adhesive composition aqueous solution can be promoted. As the heating time of the adhesive composition aqueous solution, for example, it can be 0.5 minutes to 300 minutes. If the heating time is 0.5 minutes to 300 minutes, the water contained in the adhesive composition aqueous solution can be fully evaporated.

[0093] Next, the obtained solidified material is punched (pressed) using a press machine or the like as needed, thereby forming one or more through holes on the surface of the solidified material and molding the outer shape of the solidified material into a predetermined shape (molding step). Thus, an adhesive electrode for acquiring biological signals is obtained as a molded body having a predetermined outer shape and having a through hole 11 on the surface.

[0094] In addition, the molding can be performed by a laser processing machine instead of a pressing machine. In addition, the obtained solidified material can have only through holes 11 formed on its surface, and can only have its outer shape molded into a predetermined shape. Furthermore, in the case where the solidified material can be directly used as an adhesive electrode for obtaining biological signals, the solidified material can be used as an adhesive electrode for obtaining biological signals without being molded.

[0095] Thus, the adhesive electrode for acquiring biological signals according to the present embodiment includes a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive, and the content of the nitrogen-containing additive is 0.01 wt% to 3.0 wt% relative to 100 wt% of the adhesive electrode for acquiring biological signals. By including the nitrogen-containing additive within the above range, the adhesive electrode for acquiring biological signals can absorb moisture that invades the adhesive electrode 1 for acquiring biological signals from the outside, such as sweat generated by the skin and moisture that the adhesive electrode for acquiring biological signals contacts, by using the nitrogen-containing additive, thereby improving water resistance. As a result, the adhesive electrode for acquiring biological signals can suppress the performance degradation of the aqueous emulsion adhesive, and thus can be strongly adhered to the skin. Therefore, even if the adhesive electrode for acquiring biological signals contains moisture, it can maintain substantially the same adhesiveness as before the moisture absorption (dry state).

[0096] Furthermore, the biological signal acquiring adhesive electrode can absorb water to reduce the dielectric constant and can fill the gaps generated at the interface between the biological signal acquiring adhesive electrode and the skin with water, thereby maintaining the conductivity at a high level.

[0097] Therefore, even when the biosignal acquisition adhesive electrode absorbs external moisture such as sweat generated by the skin and contains moisture during use, it can improve contact impedance and have excellent adhesiveness, thereby enabling stable measurement with high sensitivity.

[0098] Generally speaking, if the adhesiveness of an adhesive electrode is reduced, the contact impedance with respect to the skin is reduced, and the skin surface is deformed even if it is reduced due to body movement, which causes the electrode to shift and peel off, making it difficult to stably measure the biological signal. In this embodiment, the adhesive electrode for obtaining biological signals can maintain its adhesiveness even if it absorbs moisture such as sweat from the interface with the skin, so that even if the skin surface is deformed due to body movement, it can maintain a state of being attached to the skin, and the contact impedance is maintained low.

[0099] Even after the biological signal acquisition adhesive electrode is immersed in water for a predetermined time (for example, 60 seconds), the contact impedance can be suppressed from increasing and can be suppressed to a predetermined value (for example, 50 kΩ) or less.

[0100] In addition, when PEDOT / PSS is used as a conductive polymer, PSS used as a dopant in PEDOT / PSS has a high water absorption and is easy to absorb water. The adhesive electrode for acquiring biological signals contains a nitrogen-containing additive, so that the moisture present around the adhesive electrode for acquiring biological signals, such as sweat generated by the skin, is absorbed by the nitrogen-containing additive, and PSS can maintain its function as a dispersant. In addition, PSS can function as a dispersant, and PEDOT / PSS is contained in a state dispersed in the adhesive electrode for acquiring biological signals. Therefore, even if PEDOT / PSS is used as a conductive polymer, the adhesive electrode for acquiring biological signals can maintain conductivity when it contains moisture during use.

[0101] Furthermore, the bio-signal acquisition adhesive electrode contains a conductive polymer and an aqueous emulsion adhesive, so that the resistance is suppressed to a low level, and while exhibiting conductivity, it can exhibit adhesion to the skin and become soft to improve the followability to the skin surface.

[0102] The method for measuring the contact impedance of the bio-signal acquisition adhesive electrode is not particularly limited, and the contact impedance can be measured by any appropriate method. For example, a predetermined size area (for example, 4 cm 2 ) is used as a test piece, and the end of a copper foil tape of a predetermined size (for example, 5 mm in width × 10 cm in length) is attached to the end of the electrode, and the side opposite to the attached side of the copper foil tape is fixed with a cable having a clamp. The clamp on the opposite side of the cable is connected to an impedance analyzer, and the electrode is attached to a part of the subject's skin, and the contact impedance with the skin is measured for a predetermined time (for example, 1 minute). In addition, in the method for measuring the contact impedance of the adhesive electrode 1 for obtaining biological signals, the test piece of the electrode can be changed to make a biological sensor with an electrode arranged on the adhesive surface so that the electrode can contact the skin, and the contact impedance is measured using the biological sensor.

[0103] The method for measuring the adhesive force of the bio-signal acquisition adhesive electrode is not particularly limited, and the adhesive force can be measured by any appropriate method. For example, the adhesive force of the bio-signal acquisition adhesive electrode can be determined by performing a 180° peel test and measuring the 180° peel strength. 2) is prepared as a test piece, and the electrode piece is attached to a supporting substrate (for example, a PET film, etc.) and embedded to make a measurement sample. The measurement sample is cut into a predetermined size (for example, 5 cm × 1 cm), attached to an adherend (a stainless steel plate), and treated using an autoclave. Then, using a tensile testing machine, the load when the measurement sample is peeled off from the adherend is measured at a peeling angle of 180° and a predetermined peeling speed (for example, 300 mm / min), and the peeling strength (unit: N / 10mm) is calculated. Even if the electrode piece is subjected to a water absorption treatment and absorbs water, the adhesion is measured in the same manner.

[0104] When measuring the contact impedance and adhesive force of the adhesive electrode for acquiring biological signals, except when the adhesive electrode for acquiring biological signals is in a dry state, the adhesive electrode for acquiring biological signals may be subjected to a water absorption treatment and an adhesive electrode for acquiring biological signals having a predetermined water absorption rate may be used. The water absorption treatment may be performed as long as the adhesive electrode for acquiring biological signals can absorb water. For example, the water absorption rate of the adhesive electrode for acquiring biological signals may be adjusted by exposing the adhesive electrode for acquiring biological signals to a cloth containing water for a predetermined time. The water absorption rate of the adhesive electrode for acquiring biological signals may be measured by the change in the mass of the adhesive electrode for acquiring biological signals before and after the adhesive electrode for acquiring biological signals is exposed to the cloth. For example, when the mass of the adhesive electrode for acquiring biological signals increases by about 10% by mass after being exposed to the cloth for 1 second and increases by about 30% by mass after being exposed to the cloth for 3 seconds, the water absorption rate of the adhesive electrode for acquiring biological signals may be 10% by mass and 30% by mass. The water absorption rate of the bio-signal acquisition adhesive electrode can be increased from 10% by mass to 100% by mass by the mass change of the bio-signal acquisition adhesive electrode before and after water absorption, so that the bio-signal acquisition adhesive electrode having the desired absorption rate can be manufactured. In addition, the bio-signal acquisition adhesive electrode can use a cut electrode sheet.

[0105] The resistance of the adhesive electrode for acquiring biological signals can be evaluated by measuring the sheet resistance (unit: Ω / □) of the adhesive electrode for acquiring biological signals. The sheet resistance is the surface resistance of the adhesive electrode for acquiring biological signals. The sheet resistance can be measured using a general resistance measurement method, for example, it can be measured by an eddy current measurement method according to JIS Z2316-1:2014 using a non-contact resistance measuring machine. The measurement range can be a predetermined range of the main surface of the adhesive electrode for acquiring biological signals.

[0106] The adhesive electrode for acquiring biological signals can make the nitrogen content in the nitrogen-containing additive be 9wt% to 45wt% relative to the total amount of the nitrogen-containing additive. As a result, the adhesive electrode for acquiring biological signals can surely absorb moisture intruding from the outside by the nitrogen-containing additive, thereby surely improving water resistance and stably maintaining adhesiveness. As a result, the adhesive electrode for acquiring biological signals can improve contact impedance and have excellent adhesiveness even in a state where it absorbs external moisture and contains moisture.

[0107] In the adhesive electrode for acquiring biological signals, as the nitrogen-containing additive, one or more components selected from the group consisting of imidazole compounds, low molecular weight amines, and polyvinyl pyrrolidone can be used. Thus, the adhesive electrode for acquiring biological signals can surely absorb moisture intruding from the outside by the nitrogen-containing additive, thereby surely improving water resistance and stably maintaining adhesiveness. Thus, even in a state where the adhesive electrode for acquiring biological signals absorbs external moisture and contains moisture, it can improve contact impedance and have excellent adhesiveness.

[0108] In particular, the biosignal acquisition adhesive electrode contains an imidazole compound as a nitrogen-containing additive, thereby achieving flexibility and neutralization, thereby reliably reducing irritation to the skin and improving flexibility.

[0109] In the adhesive electrode for acquiring biological signals, the aqueous emulsion adhesive can use an acrylic emulsion adhesive. Thus, the adhesive electrode for acquiring biological signals can suppress the decrease in adhesive force while maintaining the resistance, and can surely improve the followability to the surface of the skin. Therefore, the adhesive electrode for acquiring biological signals can have high adhesive force and followability to the surface of the skin.

[0110] In the adhesive electrode for acquiring biological signals, the acrylic emulsion adhesive can use a silane emulsion adhesive containing a water-dispersible copolymer and an organic liquid component. As a result, the adhesive electrode for acquiring biological signals can surely suppress the viscoelasticity to a low level, thereby improving the adhesive force and further improving the followability to the surface of the skin. As a result, the adhesive electrode for acquiring biological signals can further improve the flexibility and more surely maintain the adhesiveness.

[0111] In addition, the adhesive electrode for acquiring biological signals contains glycerol as a moisturizer, so that glycerol acts as a dispersant for PEDOT used as a conductive polymer, and the dispersibility of PEDOT can be improved. In addition, glycerol can increase the crystallization of PEDOT used as a conductive polymer and improve the conductivity. Thus, the adhesive electrode for acquiring biological signals can stably improve the conductivity.

[0112] Thus, the biometric signal acquisition adhesive electrode according to the present embodiment has excellent adhesion to the skin while maintaining low contact impedance even when absorbing moisture from the outside during use, and can stably perform measurements with high sensitivity. Therefore, the biometric signal acquisition adhesive electrode can be effectively used as a biosensor, especially an adhesive biosensor electrode (biometric electrode) that requires adhesion to human skin, high flexibility, and safety to the skin.

[0113] As described above, the embodiments are described, but the embodiments are presented as examples, and the embodiments do not limit the present invention. The embodiments can be implemented in various other ways, and various combinations, omissions, substitutions, changes, etc. can be made without departing from the scope of the invention. These embodiments and their variations are included in the scope and spirit of the invention, and are included in the scope equivalent to the invention described in the claims.

[0114] Example

[0115] Hereinafter, although an Example and a comparative example are shown and embodiment is demonstrated more specifically, embodiment is not limited to these Examples and comparative examples.

[0116] <Electrode sheet production>

[0117] [Example 1]

[0118] (Preparation of Conductive Composition)

[0119] 1.0 parts by mass of PEDOT / PSS particles ("Orgacon DRY", manufactured by AGFA Materials, Japan) as a conductive polymer and 23 g of water were added to a container and stirred at a rotation speed of 2000 rpm for 10 minutes using a stirring mixer (Rentaro Bubble, Thinky Co., Ltd.). Next, 12.0 g of an emulsion adhesive (2EHA / MMA / AA / =90 / 10 / 4, solid content concentration 52%) as a binder resin, 2.0 g of glycerin as a moisturizer, and 0.1 g of an imidazole aqueous solution with an imidazole concentration of 30% as a nitrogen-containing additive were added, and the mixture was stirred and degassed at 2200 rpm for 10 minutes while mixing to prepare a uniform conductive composition aqueous solution with a solid content concentration of 24 wt%. The content of imidazole contained in the conductive composition aqueous solution was 0.8 wt% relative to the total amount of the adhesive electrode for acquiring biological signals. Furthermore, the content of nitrogen in the nitrogen-containing additive was 41 wt % based on the total amount of the nitrogen-containing additive.

[0120] (Electrode Sheet Fabrication)

[0121] The prepared conductive composition aqueous solution was applied to a polyethylene terephthalate (PET) film (PET-50-SCA1, manufactured by Fuji Corporation, 50 μm thick) surface-treated with a silicone release agent using an applicator. The PET film coated with the conductive composition aqueous solution was then transported to a drying oven (SPHH-201, manufactured by ESPEC), and the conductive composition aqueous solution was heated and dried at 130°C for 3 minutes to produce a cured product of the conductive composition. The cured product was punched (pressed) into a Figure 1 The electrode sheet (biological electrode) having a thickness of 30 μm was produced by molding into a sheet in the desired shape as shown.

[0122] [Examples 2 to 11]

[0123] In Example 1, the electrode sheet is prepared in the same manner as in Example 1 except that the nitrogen-containing additive used in the preparation of the conductive composition is changed to trimethylamine, triethylamine, triethanolamine, polyvinyl pyrrolidone or a mixture of imidazole and trimethylamine as shown in Table 1, and their contents are kept the same or changed.

[0124] [Comparative Example 1]

[0125] An electrode sheet was produced in the same manner as in Example 1 except that the nitrogen-containing additive used in the production of the conductive composition was not used.

[0126] [Comparative Example 2]

[0127] An electrode sheet was prepared in the same manner as in Example 1 except that the nitrogen-containing additive used in the preparation of the conductive composition was changed to a polyacrylic acid-based thickener (A-10H, manufactured by Toagosei Co., Ltd.).

[0128] [Comparative Example 3]

[0129] An electrode sheet was prepared in the same manner as in Example 1 except that the nitrogen-containing additive used in the preparation of the conductive composition was changed to polyvinyl pyrrolidone and the content was changed to 5 wt %.

[0130] Table 1 shows the types of nitrogen-containing additives contained in the electrode sheets in the above-mentioned respective Examples and Comparative Examples.

[0131] <Adjustment of water absorption>

[0132] A plurality of electrode sheets of each embodiment and comparative example are prepared respectively, and a part of the electrode sheets absorbs water so as to become a predetermined water absorption rate (water absorption rate). The water absorption rate of the electrode sheet is adjusted by exposing the electrode sheets of each embodiment and comparative example to a cloth containing water for a predetermined time. The mass change of the electrode sheet before and after exposure to the cloth containing water is obtained, and the water absorption rate of the electrode sheet is calculated. When the electrode sheet is exposed to the cloth containing water for 1 second, the electrode sheet increases by about 10% by mass, so the water absorption rate at this time is 10wt%. Based on the mass change of the electrode sheet when the cloth is exposed for a predetermined time, the water absorption rate of the electrode sheet is treated so as to become 10% by mass, 20% by mass, 30% by mass, 40% by mass, 50% by mass and 100% by mass, and a sample of the electrode sheet with a predetermined water absorption rate is prepared.

[0133] <Evaluation of electrode sheets>

[0134] The contact resistance, adhesive force and sheet resistance of the electrode sheets obtained in each of the examples and comparative examples were measured.

[0135] [Measurement of contact impedance]

[0136] Production area cut into 4cm 2 Electrode sheets with water absorption rates of 0 mass%, 10 mass%, 20 mass%, 30 mass% and 100 mass% were prepared. The end of a copper foil tape cut into a width of 5 mm and a length of 10 cm was bonded to the end of the prepared electrode sheet, and the opposite side of the bonding surface of the electrode sheet with the copper foil tape was fixed with a cable having an alligator clip. After connecting the clamp on the opposite side of the cable to an impedance analyzer (product name: IM3570, manufactured by Hioki Electric Co., Ltd.), the electrode sheet was bonded to the inner wrist of the subject, and the contact impedance with the skin was measured for 1 minute. The measurement results of the contact impedance of the electrode sheets of each embodiment and comparative example at each water absorption rate are shown in Table 1. In addition, the relationship between the water absorption rate and the contact impedance of the electrode sheets of each embodiment and comparative example is shown in Figure 1 .

[0137] [Adhesion]

[0138] The adhesion of the electrode sheets of each embodiment and comparative example was subjected to a 180° peel test to measure the 180° peel strength and evaluate. In addition, the adhesion was measured using electrode sheets having a water absorption of 0 mass %, 10 mass %, 20 mass %, 30 mass %, 40 mass %, 50 mass % and 100 mass %.

[0139] The electrode sheets of each embodiment and comparative example were cut into 4 cm pieces. 2An electrode sheet with an area of ​​is used as a test piece, and the electrode sheet is bonded and embedded with a PET film to prepare a measurement sample. The measurement sample is cut into a size of 5 cm × 1 cm, bonded to a stainless steel plate (SUS304BA plate) as an adherend, and treated using an autoclave. Then, using a tensile testing machine (trade name "Autoplotter AG-Xplus HS 6000mm / min high-speed model (AG-50NX plus)", manufactured by Shimadzu Corporation), the load when the measurement sample is peeled off from the adherend is measured under the peeling conditions of a peeling angle of 180° and a peeling speed (tensile speed) of 300mm / min, and the peeling strength (unit: N / 10mm) is calculated. The measurement results of the adhesive force of the electrode sheets of each embodiment and comparative example at each water absorption rate are shown in Table 2. In addition, the relationship between the water absorption rate and the adhesive force of the electrode sheets of each embodiment and comparative example is shown in Figure 2 .

[0140] [Table 1]

[0141]

[0142] [Table 2]

[0143]

[0144] From Table 1, Table 2, Figure 1 and Figure 2 In each embodiment, even if the water absorption rate is more than 30wt%, the contact impedance of the electrode sheet is suppressed to less than 68kΩ, and the adhesive force can be maintained above 2.5N / mm. In contrast, in each comparative example, the water absorption rate is 30wt%, the contact impedance exceeds 30kΩ, and the adhesive force is less than 1.5N / mm.

[0145] Thus, it is confirmed that the electrode sheets of the above-mentioned embodiments have low resistance if the predetermined amount of nitrogen-containing additives is included, and even if moisture is absorbed from the outside during use, the contact impedance can be increased while maintaining excellent adhesiveness. Therefore, even if the bio-signal acquisition adhesive electrode of the present embodiment is attached to the skin of the subject for a long time (for example, 24 hours), it does not cause a burden on the subject for a long time, and can be effectively used to stably measure bio-information.

[0146] In addition, the embodiments of the present invention are as follows, for example.

[0147] <1> An adhesive electrode for acquiring biological signals, comprising a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive.

[0148] The content of the nitrogen-containing additive is 0.01 wt % to 3.0 wt % based on the total amount of the biosignal acquiring adhesive electrode.

[0149] <2> The biological signal acquiring adhesive electrode according to <1>, wherein a content of nitrogen in the nitrogen-containing compound is 9 wt % to 45 wt % based on a total amount of the nitrogen-containing compound.

[0150] <3> The adhesive electrode for acquiring a biological signal according to <1> or <2>, wherein the nitrogen-containing additive is one or more components selected from the group consisting of imidazole compounds, triethylamine and triethanolamine. <4> The adhesive electrode for acquiring a biological signal according to any one of <1> to <3>, wherein the aqueous emulsion adhesive is an acrylic emulsion adhesive.

[0151] <5> The adhesive electrode for acquiring a biological signal according to <4>, wherein the acrylic emulsion adhesive is a silane emulsion adhesive comprising a water-dispersible copolymer and an organic liquid component compatible with the water-dispersible copolymer.

[0152] <6> A biosensor comprising the biosignal acquisition adhesive electrode according to any one of <1> to <5>.

[0153] This application claims priority based on Japanese Patent Application No. 2022-153422 filed with the Japan Patent Office on September 27, 2022, and cites all the contents described in the above application.

Claims

1. An adhesive electrode for acquiring biological signals, comprising a conductive polymer, an aqueous emulsion adhesive, and a nitrogen-containing additive. The content of the nitrogen-containing additive is 0.01 wt % to 3.0 wt % based on the total amount of the biosignal acquiring adhesive electrode.

2. The adhesive electrode for acquiring biological signals according to claim 1, The nitrogen content in the nitrogen-containing additive is 9 wt % to 45 wt % based on the total amount of the nitrogen-containing additive.

3. The adhesive electrode for acquiring biological signals according to claim 1, The nitrogen-containing additive is one or more components selected from the group consisting of imidazole compounds, low molecular weight amines and polyvinyl pyrrolidone.

4. The adhesive electrode for acquiring biological signals according to claim 1, The water-based emulsion adhesive is an acrylic emulsion adhesive.

5. The adhesive electrode for acquiring biological signals according to claim 4, The acrylic emulsion adhesive is a silane emulsion adhesive including a water-dispersible copolymer and an organic liquid component compatible with the water-dispersible copolymer. 6 . A biosensor comprising the biosignal acquisition adhesive electrode according to claim 1 .

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