Patent Description:
Conventionally, a biosensor that is attached to the skin of a living body such as humans and detects biosignals has been known.

For such a biosensor, for example, Patent Document <NUM> has proposed a biocompatible polymer substrate including an adhesive first layer; a second layer disposed on an upper face thereof; an electrode that is disposed at a lower face of the second layer and makes contact with skin, a data input module disposed on the upper face of the first layer, and a wire disposed on the upper face of the second layer and connecting the electrode and module.

In such a biocompatible polymer substrate, the first layer is attached to the human skin, the electrode makes contact with the skin and detects the biosignals, such as voltage signals from the heart muscles via the skin, and the data input module receives and records the voltage signals from the heart muscles.

Further related art may be found in <CIT> which discloses a tab style electrode, in <CIT> which discloses an electrode for biological information measurement and in <CIT> which discloses a method of providing an imaging system and imaging system thereof.

Meanwhile, when the surface of the electrode that is making contact with the skin of a living body gets dry, the electrode impedance rises to increase noises. Therefore, it has been examined to moisturize the interface between the electrode and skin with moisture to make lower electrode impedance.

However, when the biosensor is attached to the skin of a living body and used for a long period of time, the moisture steadily permeates into the biosensor and evaporates, and the electrode surface gets dry non-uniformly. As a result, an excessive increase and a large variation in the electrode impedance disadvantageously occur.

The present invention provides a laminate for biosensor and a biosensor that suppress increase and variation in electrode impedance.

The present invention is defined by the appended independent claim. The dependent claims describe optional features and distinct embodiments.

The present invention [<NUM>] includes a laminate for biosensor including a pressure-sensitive adhesive layer for attaching to a living body; and a substrate layer disposed on the upper face of the pressure-sensitive adhesive layer, wherein the laminate for biosensor includes a probe disposed at the lower face of the laminate for biosensor, and a moisture barrier layer disposed so as to overlap with the probe when projected in the thickness direction.

With this laminate for biosensor, the moisture barrier layer is disposed so as to overlap with the probe. Therefore, when the laminate for biosensor is attached to the skin of a living body, the moisture barrier layer can suppress moisture present at the interface between the living body and the probe to permeate the laminate for biosensor in the thickness direction. As a result, the moisture can be kept uniformly at the lower face of the probe, and dryness of the probe can be suppressed uniformly. Therefore, increase and variation in the electrode impedance can be suppressed.

The present invention [<NUM>] includes the laminate for biosensor of [<NUM>], wherein the moisture barrier layer has a moisture permeability of <NUM>/m<NUM>·day or less.

With this laminate for biosensor, the moisture barrier layer has a low moisture permeability, and therefore increase in impedance and impedance variation can be suppressed even more reliably.

The present invention [<NUM>] includes the laminate for biosensor of [<NUM>] or [<NUM>], wherein the moisture barrier layer is disposed at a side upper than the lower face of the probe.

With this laminate for biosensor, the moisture barrier layer is disposed at a side upper than the lower face of the probe. Therefore, compared with the laminate for biosensor, in which the moisture barrier layer is disposed at the side lower than the lower face of the probe, the material of the moisture barrier layer can be selected more freely, and a material with high moisture barrier properties can be selected. Furthermore, the entire lower face of the laminate for biosensor can be made flat, and therefore it can be attached to a living body excellently.

The present invention [<NUM>] includes the laminate for biosensor of any one of [<NUM>] to [<NUM>], wherein the moisture barrier layer is disposed inside the pressure-sensitive adhesive layer.

With this laminate for biosensor, the moisture barrier layer is disposed inside the pressure-sensitive adhesive layer, and therefore the moisture barrier layer is disposed at a position near the probe. Therefore, the moisture can be kept uniformly and more reliably at the lower face of the probe.

The present invention [<NUM>] includes the laminate for biosensor of [<NUM>], wherein the moisture barrier layer has pressure-sensitive adhesiveness.

With this laminate for biosensor, the moisture barrier layer has pressure-sensitive adhesiveness, and therefore can adhere to the probe and the substrate layer pressure-sensitively; and detachment of the moisture barrier layer can be reliably suppressed. When the probe has an exposure region, the lower face of the moisture barrier layer can be exposed at the exposure region of the probe, and attached to a living body with pressure-sensitive adhesion. Therefore, the probe can be reliably brought into contact with a living body uniformly, and more reliable sensing can be achieved.

The present invention [<NUM>] includes the laminate for biosensor of any one of [<NUM>] to [<NUM>], wherein the moisture barrier layer is disposed at the upper side of the substrate layer.

With this laminate for biosensor, the moisture barrier layer is disposed at the upper side of the substrate layer, and therefore the moisture barrier layer can be easily disposed at the upper side of the substrate layer through the pressure-sensitive adhesive layer. Therefore, it is excellently suitable for production.

The present invention [<NUM>] includes the laminate for biosensor of any one of [<NUM>] to [<NUM>], wherein the moisture barrier layer is at least one resin layer selected from the group consisting of a rubber resin layer, polystyrene resin layer, polyolefin resin layer, acrylic resin layer, and poly vinyl alcohol resin layer.

With this laminate for biosensor, the moisture barrier layer is a specific resin layer, and therefore increase in impedance and impedance variation can be more reliably suppressed.

The present invention [<NUM>] includes the laminate for biosensor of any one of [<NUM>] to [<NUM>], wherein the probe has an exposure region that allows the pressure-sensitive adhesive layer or the moisture barrier layer to be exposed.

With this laminate for biosensor, the probe has an exposure region, so that the pressure-sensitive adhesive layer or the moisture barrier layer having pressure-sensitive adhesiveness is allowed to be exposed at the exposure region in the lower face side of the laminate for biosensor. Therefore, the entire probe can be brought into contact with a living body. As a result, more reliable sensing can be achieved.

The present invention [<NUM>] includes a biosensor including the laminates for biosensor of any one of [<NUM>] to [<NUM>]; and an electronic component that is electrically connected to the probe, and mounted on the substrate layer.

With this biosensor, the laminate for biosensor described above is included, and therefore increase in impedance and impedance variation of the biosensor can be suppressed.

The laminate for biosensor and biosensor of the present invention can suppress increase and variation in electrode impedance of the biosensor.

In <FIG>, left-right direction on the sheet is longitudinal direction (first direction) of the biosensor laminate <NUM>, laminate for biosensor. Right side on the sheet is longitudinal one side (one side in first direction), left side on the sheet is longitudinal other side (the other side in first direction).

In <FIG>, up-down direction on the sheet is a latitudinal direction (direction orthogonal to longitudinal direction, width direction, second direction orthogonal to first direction) of the biosensor laminate <NUM>. Upper side on the sheet is one side in latitudinal direction (one side in width direction, one side in second direction), and lower side on the sheet is the other side in latitudinal direction (the other side in width direction, the other side in second direction).

In <FIG>, paper thickness direction on the sheet is up-down direction (thickness direction, third direction orthogonal to first direction and second direction) of the biosensor laminate <NUM>. Near side on the sheet is upper side (one side in thickness direction, one side in third direction), and far side on the sheet is lower side (the other side in thickness direction, the other side in third direction). The directions are in accordance with the direction arrows described in the figures.

These definitions of the directions are not intended to limit the orientations of the biosensor laminate <NUM> and wearable electrocardiograph <NUM> (described later) at the time of production and use.

A first embodiment of the laminate for biosensor of the present invention is described with reference to <FIG>.

As shown in <FIG>, a biosensor laminate <NUM>, laminate for biosensor, in one embodiment of the first embodiment has generally a flat plate shape extending in longitudinal direction. The biosensor laminate <NUM> includes a pressure-sensitive adhesive layer <NUM>, a moisture barrier layer <NUM>, a substrate layer <NUM>, a wire layer <NUM>, a probe <NUM>, and a connecter <NUM>. To be specific, the biosensor laminate <NUM> includes a pressure-sensitive adhesive layer <NUM>, a moisture barrier layer <NUM> disposed inside the pressure-sensitive adhesive layer <NUM>, a substrate layer <NUM> disposed at the upper side of the pressure-sensitive adhesive layer <NUM> and moisture barrier layer <NUM>, a wire layer <NUM> embedded in the substrate layer <NUM>, a probe <NUM> embedded in the moisture barrier layer <NUM>, and a connecter <NUM> that electrically connects the wire layer <NUM> and the probe <NUM>.

The pressure-sensitive adhesive layer <NUM> is a layer that gives pressure-sensitive adhesiveness to the lower face of the biosensor laminate <NUM> for attaching the lower face of the biosensor laminate <NUM> to the surface, such as skin <NUM>, of a living body.

The pressure-sensitive adhesive layer <NUM> forms, as shown in <FIG>, along with the moisture barrier layer <NUM> and probe <NUM> to be described later, the lower face of the biosensor laminate <NUM>. The pressure-sensitive adhesive layer <NUM> forms the contour of the part of biosensor laminate <NUM>. The pressure-sensitive adhesive layer <NUM> has a flat plate shape (sheet shape) extending in longitudinal direction. To be specific, the pressure-sensitive adhesive layer <NUM> has, for example, a band shape extending in longitudinal direction, with a longitudinal center portion bulging toward latitudinal both outsides. In the pressure-sensitive adhesive layer <NUM>, both end edges in latitudinal direction of the longitudinal center portion are positioned at latitudinal both outsides relative to the both end edges in latitudinal direction of other than the longitudinal center portion.

The pressure-sensitive adhesive layer <NUM> has an adhesion opening <NUM> at each of the both end portions, in longitudinal direction, of the layer <NUM>. The two adhesion openings <NUM> each has a generally rectangular shape (square shape) in plan view, and penetrates the pressure-sensitive adhesive layer <NUM> in the thickness direction. The moisture barrier layer <NUM> and the connecter <NUM> (described later) are disposed in the adhesion opening <NUM>.

The pressure-sensitive adhesive layer <NUM> has a moisture permeability of, for example, <NUM>/m<NUM>·day or more, preferably <NUM>/m<NUM>·day or more, and for example, <NUM>/m<NUM>·day or less. When the pressure-sensitive adhesive layer <NUM> has a moisture permeability of the above-described lower limit or more, when the biosensor laminate <NUM> is attached to a living body, the sweat generated from the living body can appropriately permeate through the layer <NUM> to the outside of the biosensor laminate <NUM> to reduce uncomfortableness (steaming, etc.) felt by the living body. Therefore, it has excellent wearability.

In the present invention, the moisture permeability of layers such as the pressure-sensitive adhesive layer <NUM> is calculated based on the following steps.

The materials for the pressure-sensitive adhesive layer <NUM> are those materials having pressure-sensitive adhesiveness, and, preferably, also having biocompatibility. Examples of such a material include acrylic pressure-sensitive adhesive, and silicone pressure-sensitive adhesive, and preferably, acrylic pressure-sensitive adhesive is used.

The acrylic pressure-sensitive adhesive (acrylic pressure-sensitive adhesive composition) contains acrylic polymer.

The acrylic polymer is a main component of the acrylic pressure-sensitive adhesive, and is a pressure-sensitive adhesive component.

The acrylic polymer is a polymer produced by polymerizing monomer components containing (meth)acrylic ester (to be specific, acrylic acid isononyl, acrylic acid methoxy ethyl, etc.) as a main component (content <NUM> mass% or more, <NUM> mass% or less in the monomer components), and other monomer (to be specific, acrylic acid, etc.) that is copolymerizable with (meth)acrylic ester as an optional component (content <NUM> mass% or less, <NUM> mass% or more in the monomer components). Examples of the acrylic polymer include acrylic polymer described in <CIT>.

The acrylic pressure-sensitive adhesive preferably further contains carboxylic acid ester.

Carboxylic acid ester in the acrylic pressure-sensitive adhesive is a pressure-sensitive adhesive strength adjustor that reduces the pressure-sensitive adhesive strength of the acrylic polymer, and adjusts the pressure-sensitive adhesive strength of the pressure-sensitive adhesive layer <NUM>. Carboxylic acid ester is carboxylic acid ester miscible with acrylic polymer.

Examples of the carboxylic acid ester include ester of carboxylic acid (fatty acid) with trihydric alcohol, such as capric triglyceride, capric monoglyceride, tri-<NUM>-ethyl hexanoic acid glyceryl, tri capric acid glyceryl, tri lauric acid glyceryl, glyceryl triisostearate, tri oleic acid glyceryl, and tri-<NUM>-ethyl hexanoic acid trimethylolpropane; ester of carboxylic acid with dihydric alcohol, such as propylene glycol dicaprylate, propylene glycol dicaprate, and propylene glycol diisostearate; and ester of carboxylic acid with monohydric alcohol, such as myristic acid ethyl, myristic acid isopropyl, palmitic acid isopropyl, stearic acid butyl, isostearic acid isopropyl, lauric acid hexyl, phthalic acid diethyl, dioctyl phthalate, myristic acid stearyl, oleic acid stearyl, cetyl dimethyl octanoate, cetyl <NUM>-ethyl hexanoate, isocetyl <NUM>-ethyl hexanoate, <NUM>-ethyl hexanoic acid stearyl, and succinic acid dioctyl. Examples of carboxylic acid ester further include cetyl lactate and myristyl lactate. These carboxylic acid esters can be used singly, or can be used in combination.

For the carboxylic acid ester, preferably, an ester of fatty acid and trihydric alcohol is used, more preferably, in view of compatibility, an ester of fatty acid and glycerine is used, even more preferably, capric triglyceride is used.

The carboxylic acid ester content relative to <NUM> parts by mass of acrylic polymer is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

The acrylic pressure-sensitive adhesive can contain, as necessary, a cross-linking agent. The cross-linking agent is a crosslinking component that crosslinks acrylic polymer. Examples of the cross-linking agent include a polyisocyanate compound, epoxy compound, melamine compound, peroxide compound, urea compound, metal alkoxide compound, metal chelate compound, metal salt compound, carbodiimide compound, oxazoline compound, aziridine compound, and amine compound. These cross-linking agents can be used singly, or can be used in combination. For the cross-linking agent, preferably, a polyisocyanate compound (polyfunctional isocyanate compound) is used.

The cross-linking agent content relative to <NUM> parts by mass of acrylic polymer is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> part by mass or less.

The pressure-sensitive adhesive layer <NUM> has a thickness (excluding the region of adhesion groove <NUM>) of, for example, <NUM> or more, preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less, more preferably <NUM> or less.

The moisture barrier layer <NUM> is a barrier layer that suppresses moisture present surrounding the probe <NUM> to be described later to permeate the biosensor laminate <NUM> in the thickness direction. In this manner, moisture is kept at the interface between the lower face of the probe <NUM> and the skin <NUM> of a living body.

The moisture barrier layer <NUM> forms, as shown in <FIG>, the lower face of the biosensor laminate <NUM> along with the pressure-sensitive adhesive layer <NUM>. The moisture barrier layer <NUM> has, in plan view, a generally rectangular shape slightly smaller than the adhesion opening <NUM>, and has a flat plate shape (sheet shape).

The moisture barrier layer <NUM> is disposed inside the adhesion opening <NUM> of the pressure-sensitive adhesive layer <NUM>. The peripheral face of the moisture barrier layer <NUM> is, over the entire circumference, in spaced apart relation with the inner periphery of the adhesion opening <NUM>. That is, the pressure-sensitive adhesive layer <NUM> and the moisture barrier layer <NUM> define a frame adhesion opening <NUM> having a generally rectangular frame shape in plan view. The frame adhesion opening <NUM> is filled with a connecter <NUM> to be described later.

The moisture barrier layer <NUM> is disposed so as to overlap with the probe <NUM> to be described later when projected in the thickness direction. To be specific, the moisture barrier layer <NUM> is disposed so that the contour of the moisture barrier layer <NUM> is coincide with the contour of the probe <NUM> (also with the inner shape of the connecter <NUM>) when projected in the thickness direction. That is, the contour of the moisture barrier layer <NUM> is the same as the contour of the probe <NUM> in plan view. The moisture barrier layer <NUM> is disposed above the probe <NUM>. The lower face of the moisture barrier layer <NUM> has an adhesion groove <NUM> corresponding to the probe <NUM> (described later), and the probe <NUM> is embedded in the moisture barrier layer <NUM> at the adhesion groove <NUM>. In this manner, the moisture barrier layer <NUM> makes contact with the substrate layer <NUM>, probe <NUM>, and connecter <NUM>.

The moisture barrier layer <NUM> has a moisture permeability lower than the moisture permeability of the pressure-sensitive adhesive layer <NUM> and substrate layer <NUM>. To be specific, the moisture barrier layer <NUM> has a moisture permeability of, for example, below <NUM>/m<NUM>·day, preferably <NUM>/m<NUM>·day or less, more preferably <NUM>/m<NUM>·day or less, even more preferably <NUM>/m<NUM>·day or less, and for example, <NUM>/m<NUM>·day or more.

For the material of the moisture barrier layer <NUM>, for example, resin is used. To be specific, examples of the moisture barrier layer <NUM> include resin layers such as a rubber resin layer (polyisobutylene resin layer, butyl rubber resin layer, SBR resin layer, natural rubber / SBR resin layer, etc.), polystyrene resin layer, polyolefin resin layer (polypropylene resin layer, polyethylene resin layer, etc.), acrylic resin layer, and poly vinyl alcohol resin layer. These resin layers can be used singly, or can be used in combination of two or more.

The moisture barrier layer <NUM> can include, for example, foam. That is, the resin layer can be a resin foam layer such as a polypropylene foam layer and acrylic foam layer.

Preferably, the moisture barrier layer <NUM> has pressure-sensitive adhesiveness. For the moisture barrier layer of the pressure-sensitive adhesiveness, preferably, a rubber resin layer (rubber pressure-sensitive adhesive layer), more preferably, a polyisobutylene resin layer (polyisobutylene pressure-sensitive adhesive layer) is used.

The polyisobutylene resin layer is formed from a polyisobutylene composition. The polyisobutylene composition contains, as a rubber component, polyisobutylene. The polyisobutylene composition has a polyisobutylene content of, for example, <NUM> mass% or more, preferably <NUM> mass% or more, and for example, <NUM> mass% or less, preferably <NUM> mass% or less.

The polyisobutylene composition preferably contains a superabsorbent polymer and tackifier. In this manner, excellent moisture barrier properties and pressure-sensitive adhesiveness can be given to the rubber composition such as a polyisobutylene composition.

Examples of the superabsorbent polymer include maleic anhydride salt resin (for example, crosslinked sodium salt of isobutylene-maleic anhydride copolymer, etc.), polyacrylate resin, polysulfonate resin, poly acrylamide resin, and poly vinyl alcohol resin; and preferably, maleic anhydride salt resin is used. The superabsorbent polymer content relative to <NUM> parts by mass of polyisobutylene is, for example, <NUM> part by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

Examples of the tackifier include rosin resin, terpene resin (for example, terpene-aromatic liquid resin, etc.), coumarone-indene resin, phenol resin, phenol-formaldehyde resin, xylene formalin resin, and petroleum resin (for example, C5 petroleum resin, C9 petroleum resin, C5/C9 petroleum resin, etc.), and preferably, petroleum resin is used. The tackifier content relative to <NUM> parts by mass of polyisobutylene is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

The polyisobutylene composition further contains, as necessary, a softener, filler, and cross-linking agent.

Examples of the softener include liquid rubber such as polybutene, liquid isoprene rubber, and liquid butadiene rubber; oils such as paraffin oil and naphthene oil; and esters such as phthalic acid ester and phosphoric acid ester, and preferably, liquid rubber is used. The softener content relative to <NUM> parts by mass of polyisobutylene is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

Examples of the filler include calcium carbonate (for example, calcium carbonate heavy, calcium carbonate light, and Hakuenka), carbon black, talc, mica, clay, mica powder, bentonite, silica, alumina, aluminum silicate, titanium oxide, metal powder (for example, aluminum powder, iron powder, etc.), resin powder (for example, acrylic resin powder, styrene resin powder, etc.), glass powder, boron nitride powder, and metalhydroxide (for example, aluminum hydroxide, magnesium hydroxide, etc.); and preferably, calcium carbonate is used. The filler content relative to <NUM> parts by mass of polyisobutylene is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

Examples of the cross-linking agent include isocyanate compounds such as hexamethylene diisocyanate. The cross-linking agent content relative to <NUM> parts by mass of polyisobutylene is, for example, <NUM> part by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

The polyisobutylene composition may also contain known additives such as a foaming agent and a plasticizer at a suitable ratio.

Of those examples of the rubber resin layer (rubber pressure-sensitive adhesive layer), in view of stable attachment to the skin, preferably, the SBR resin layer, natural rubber-SBR resin layer are used, and more preferably, the SBR resin layer is used.

The SBR resin layer is formed from a styrene-butadiene rubber (SBR) composition. The SBR composition contains SBR as a rubber component. The SBR composition has an SBR content of, for example, <NUM> mass% or more, preferably <NUM> mass% or more, and for example, <NUM> mass% or less, preferably <NUM> mass% or less.

The SBR composition may also contain a superabsorbent polymer, tackifier, softener, filler, and cross-linking agent, as in the case with the polyisobutylene composition.

The natural rubber-SBR resin layer is formed from a natural rubber/SBR composition. The natural rubber-SBR composition contains natural rubber and SBR as a rubber component. In the natural rubber-SBR composition, the natural rubber and SBR contents in total is, for example, <NUM> mass% or more, preferably <NUM> mass% or more, and for example, <NUM> mass% or less, preferably <NUM> mass% or less.

The natural rubber-SBR composition may also contain a superabsorbent polymer, tackifier, softener, filler, and cross-linking agent, as in the case with the polyisobutylene composition.

The moisture barrier layer <NUM> has a thickness that is substantially the same as the thickness of the pressure-sensitive adhesive layer <NUM>. To be specific, the moisture barrier layer <NUM> has a thickness of, for example, <NUM> or more, preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less, more preferably <NUM> or less.

When the biosensor laminate <NUM> is projected in the thickness direction, the region where the moisture barrier layer <NUM> is present is referred to as a barrier region <NUM>, and the region other than the barrier region <NUM> is referred to as a non-barrier region <NUM>. That is, the biosensor laminate <NUM> includes two barrier regions <NUM> disposed at both sides in longitudinal direction, and one continuous non-barrier region <NUM>.

The barrier region <NUM> is smaller than the non-barrier region <NUM>. To be specific, the ratio (A2/A1) of area A2 of the non-barrier region <NUM> relative to the area A1 of the barrier region <NUM> is, for example, <NUM> or more, preferably <NUM> or more, more preferably <NUM> or more, and for example, <NUM> or less. The barrier regions <NUM> have an area A1 of, for example, <NUM>. <NUM><NUM> or more, preferably <NUM><NUM> or more, more preferably <NUM><NUM> or more, and for example, <NUM><NUM> or less, preferably <NUM><NUM> or less, more preferably <NUM><NUM> or less. When the above-described ratio is the above-described lower limit or more, or the area of the barrier region <NUM> is the above-described upper limit or less, the area ratio of the non-barrier region <NUM> can be increased, and wearability of the biosensor laminate <NUM> will be more excellent.

The substrate layer <NUM> is a support layer that supports the pressure-sensitive adhesive layer <NUM> and moisture barrier layer <NUM>.

The substrate layer <NUM> forms the upper face of the biosensor laminate <NUM>, as shown in <FIG>. The substrate layer <NUM> forms the contour of the biosensor laminate <NUM> along with the pressure-sensitive adhesive layer <NUM>. The contour of the substrate layer <NUM> in plan view is the same as the contour of the pressure-sensitive adhesive layer <NUM> in plan view. The substrate layer <NUM> is disposed at the entire upper face of the pressure-sensitive adhesive layer <NUM> and moisture barrier layer <NUM>. The substrate layer <NUM> has a sheet shape extending in longitudinal direction.

On the upper face of the substrate layer <NUM>, as shown in <FIG>, a substrate groove <NUM> corresponding to the wire layer <NUM> is formed. The substrate groove <NUM> has the same pattern shape as the wire layer <NUM> in plan view. The substrate groove <NUM> is opened upward.

The substrate layer <NUM> has a frame substrate opening <NUM> corresponding to the frame adhesion opening <NUM>. The frame substrate opening <NUM> communicates with the frame adhesion opening <NUM> in the thickness direction. The frame substrate opening <NUM> has a generally rectangular frame shape, in plan view, having the same shape and size as that of the frame adhesion opening <NUM>.

The substrate layer <NUM> has a moisture permeability of, for example, <NUM>/m<NUM>·day or more, preferably <NUM>/m<NUM>·day or more, and for example, <NUM>/m<NUM>·day or less. When the substrate layer <NUM> has a moisture permeability of the above-described lower limit or more, when the biosensor laminate <NUM> is attached to a living body, sweat generated by the living body is allowed to appropriately permeate through the biosensor laminate <NUM> to the outside, and uncomfortableness (steaming, etc.) felt by the living body can be decreased. Therefore, it has excellent wearability.

The substrate layer <NUM> has an elongation at break of, for example, <NUM>% or more, preferably <NUM>% or more, more preferably <NUM>% or more, and for example, <NUM>% or less. The elongation at break is measured based on JIS K <NUM>(<NUM>), with a tensile speed of <NUM>/min and a test piece type <NUM>.

The substrate layer <NUM> has a tensile strength at <NUM> (between chucks <NUM>, tensile speed <NUM>/min, strength at break) of, for example, <NUM> N/<NUM> or more, preferably <NUM> N/<NUM> or more, and for example, <NUM> N/<NUM> or less. The tensile strength is measured based on JIS K <NUM>(<NUM>).

The substrate layer <NUM> has a tensile storage modulus E' at <NUM> of, for example, <NUM> MPa or less, preferably <NUM> MPa or less, more preferably <NUM> MPa or less, even more preferably <NUM> MPa or less, particularly preferably <NUM> MPa or less, and for example, <NUM> MPa or more. The tensile storage modulus E' at <NUM> is obtained by subjecting the substrate layer <NUM> to dynamic viscoelasticity measurement under conditions of a frequency <NUM> and a temperature increase speed of <NUM>/min.

The material of the substrate layer <NUM> has stretching property when it satisfies at least one, preferably two or more, more preferably all of three of the following conditions: (<NUM>) elongation at break is <NUM>% or more, (<NUM>) tensile strength is <NUM> N/<NUM> or less, and (<NUM>) tensile storage modulus E' is <NUM> MPa or less.

The substrate layer <NUM> is formed from a substrate composition. The substrate composition contains a substrate resin.

The substrate resin is a main component of the substrate composition, and for example, it is a flexibility resin that gives the substrate layer <NUM> appropriate stretching property, flexibility, and tenacity.

Examples of the substrate resin include thermoplastic resin such as polyurethane resin, silicone resin, polystyrene resin, vinyl chloride resin, and polyester resin. Preferably, polyurethane resin is used. In this manner, the substrate layer <NUM> can have more excellent stretching property.

The substrate composition (substrate layer <NUM>) has a substrate resin content of, for example, <NUM> mass% or more, preferably <NUM> mass% or more, and for example, <NUM> mass% or less, preferably <NUM> mass% or less.

The substrate composition further contains, preferably, carboxylic acid ester. Carboxylic acid ester in the substrate composition is an elasticity modifier that gives flexibility to the biosensor laminate <NUM>.

To be specific, those carboxylic acid esters given as examples for the pressure-sensitive adhesive of the pressure-sensitive adhesive layer <NUM> can be used, and preferably, tri fatty acid glyceryl is used.

The carboxylic acid ester content relative to <NUM> parts by mass of the substrate resin is, for example, <NUM> parts by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less. The substrate composition (substrate layer <NUM>) has a carboxylic acid ester content of, for example, <NUM> mass% or more, preferably <NUM> mass% or more, and for example, <NUM> mass% or less, preferably <NUM> mass% or less.

The substrate layer <NUM> has a thickness (excluding the region of the substrate groove <NUM>) of, for example, <NUM> or more, preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less, preferably <NUM> or less. When the substrate layer <NUM> has a thickness of the above-described lower limit or more, the substrate layer <NUM> can reliably keep its shape, and therefore handleability of the biosensor laminate <NUM> is excellent. When the substrate layer <NUM> has a thickness of the above-described upper limit or less, the substrate layer <NUM> can be attached to the living body reliably.

As shown in <FIG>, the wire layer <NUM> is embedded in the substrate groove <NUM> of the substrate layer <NUM>. To be specific, the wire layer <NUM> is embedded in the upper end portion of the substrate layer <NUM> so as to be exposed from the upper face of the substrate layer <NUM>. The entire lower face and the entire side face of the wire layer <NUM> is in contact with the substrate layer <NUM>. The upper face of the wire layer <NUM> is exposed from the upper face (excluding the substrate groove <NUM>) of the substrate layer <NUM>. The upper face of the wire layer <NUM> forms the upper face of the biosensor laminate <NUM> along with the upper face of the substrate layer <NUM>, and the upper face of the wire layer <NUM> is flush with the upper face of the substrate layer <NUM>.

As shown in <FIG>, the wire layer <NUM> has a wire pattern connecting the connecter <NUM> with the electronic component <NUM> (described later) and battery <NUM> (described later). To be specific, the wire layer <NUM> includes a first wire pattern <NUM> and a second wire pattern <NUM> independently.

The first wire pattern <NUM> is disposed at one side in longitudinal direction of the substrate layer <NUM>. The first wire pattern <NUM> includes a first wire 16A and a first terminal 17A and a second terminal 17B continuous thereto.

The first wire pattern <NUM> has generally a T-shape in plan view. To be specific, the first wire pattern <NUM> extends from longitudinal one end portion of the substrate layer <NUM> to longitudinal other side, and branches out at a center portion in the longitudinal direction of the substrate layer <NUM> and extends toward both outsides in latitudinal direction.

The first terminal 17A and the second terminal 17B are disposed at latitudinal both end portions at a center portion in the longitudinal direction of the substrate layer <NUM>. The first terminal 17A and the second terminal 17B each has a substantially rectangular shape in plan view (land shape). The first terminal 17A and the second terminal 17B is each continuous with one of the both end portions of the first wire 16A extending toward both outside in the latitudinal direction at a center portion in the longitudinal direction of the substrate layer <NUM>.

The second wire pattern <NUM> is provided at the other side in the longitudinal direction of the first wire pattern <NUM> in spaced apart relation. The second wire pattern <NUM> includes a second wire 16B and a third terminal 17C and a fourth terminal 17D continuous thereto.

The second wire pattern <NUM> has a generally T-shape in plan view. To be specific, the second wire pattern <NUM> extends from the other end portion in the longitudinal direction of the substrate layer <NUM> toward one side in longitudinal direction, branches out at a center portion in the longitudinal direction of the substrate layer <NUM> and extend toward both outside in the latitudinal direction.

The third terminal 17C and fourth terminal 17D are disposed at latitudinal both end portions at a center portion in the longitudinal direction of the substrate layer <NUM>. The third terminal 17C and the fourth terminal 17D each has a substantially rectangular shape in plan view (land shape). The third terminal 17C and the fourth terminal 17D is each continuous with one of the both end portions of the second wire 16B extending toward both outsides in the latitudinal direction at a center portion in the longitudinal direction of the substrate layer <NUM>.

For the material of the wire layer <NUM>, for example, metal conductors such as copper, nickel, gold, and alloys thereof are used, and preferably, copper is used.

The wire layer <NUM> has a thickness of, for example, <NUM> or more, preferably <NUM> or more, and for example, less than <NUM>, preferably <NUM> or less, more preferably <NUM> or less.

The probe <NUM> is an electrode that detects a signal or signals, such as electric signals, temperatures, vibrations, sweat, and metabolites, of a living body when the pressure-sensitive adhesive layer <NUM> is attached to the surface of a living body, making contact with the surface of the living body.

As shown in <FIG>, the probe <NUM> is embedded in the adhesion groove <NUM> of the moisture barrier layer <NUM>. To be specific, the probe <NUM> is embedded in the lower end portion of the moisture barrier layer <NUM> so as to be exposed from the lower face of the moisture barrier layer <NUM> inside the connecter <NUM>. The entire upper face and the entire side face of the probe <NUM> are in contact with the moisture barrier layer <NUM>. The lower face of the probe <NUM> is exposed at the lower face of the moisture barrier layer <NUM> (excluding the adhesion groove <NUM>). The lower face of the probe <NUM> forms the lower face of the biosensor laminate <NUM> along with the lower face of the moisture barrier layer <NUM> and pressure-sensitive adhesive layer <NUM>, and the lower face of the probe <NUM> is flush with the lower face of the moisture barrier layer <NUM>.

The probe <NUM> has a shape that includes an exposure region <NUM> that allows the moisture barrier layer <NUM> to be exposed at the lower face of the biosensor laminate <NUM>. The probe <NUM> has, for example, a mesh shape in plan view. To be specific, the contour of the probe <NUM> (that is, inner shape of the connecter <NUM>) has a generally rectangular shape in plan view, and the inner side of the probe <NUM> has a grid shape in plan view. The lower face of the moisture barrier layer <NUM> is exposed at the gaps of the grid shape in plan view (exposure region <NUM>).

Examples of the material of the probe <NUM> include an electrically conductive resin composition, and metal conductors given as examples for the wire layer <NUM>; and preferably, an electrically conductive resin composition is used.

The electrically conductive resin composition contains, for example, electrically conductive polymers and resin components.

Examples of the electrically conductive polymer include polyaniline, polypyrrole, polythiophene, poly (ethylenedioxythiophene) (PEDOT), poly (ethylenedioxythiophene)-polystyrene sulfonate (PEDOT-PSS).

Examples of the resin component include poly vinyl alcohol resin, polyester resin, polyurethane resin, acrylic resin, vinyl resin, epoxy resin, and amide resin.

Known additives such as a cross-linking agent, plasticizer, and surfactant may be contained in the resin component other than the above-described resin.

The electrically conductive polymer content relative to <NUM> parts by mass of the resin component is, for example, <NUM> part by mass or more, preferably <NUM> parts by mass or more, and for example, <NUM> parts by mass or less, preferably <NUM> parts by mass or less.

For the method for forming a probe <NUM> using the electrically conductive resin composition, the method described in <CIT> is used.

The area A3 of the probe region <NUM> is substantially the same as the area A1 of the barrier region <NUM>, to be specific, for example, <NUM><NUM> or more, preferably <NUM><NUM> or more, more preferably <NUM><NUM> or more, and for example, <NUM><NUM> or less, preferably <NUM><NUM> or less, more preferably <NUM><NUM> or less. The probe region <NUM> is a region surrounded by the contour of the probe <NUM> (also the inner periphery of the connecter <NUM>) in plan view.

The probe <NUM> has a thickness of, for example, <NUM> or more, preferably <NUM> or more, and for example, less than <NUM>, preferably <NUM> or less, more preferably <NUM> or less.

As shown in <FIG>, the connecter <NUM> is provided in correspondence with the frame substrate opening <NUM> and the frame adhesion opening <NUM>, and has the same shape as those. The connecter <NUM> penetrates (passes through) the biosensor laminate <NUM> in the thickness direction (up-down direction), and fills the frame substrate opening <NUM> and the frame adhesion opening <NUM>. The connecter <NUM> has a substantially hollow prism shape with its axis extending in the thickness direction.

The internal face of the connecter <NUM> is in contact with the probe <NUM>, moisture barrier layer <NUM>, and the substrate layer <NUM> inside the frame substrate opening <NUM>. The external face of the connecter <NUM> is in contact with the wire layer <NUM> (first wire 16A, first wire 16B), pressure-sensitive adhesive layer <NUM>, and the substrate layer <NUM> outside the frame substrate opening <NUM>. In this manner, the connecter <NUM> electrically connects the wire layer <NUM> and probe <NUM>.

For the material of the connecter <NUM>, the above-described metal conductor and electrically conductive resin (including electrically conductive polymer) are used, and preferably, electrically conductive resin is used.

Next, description is given below of the method for producing a biosensor laminate <NUM> in one embodiment with reference to <FIG>.

As shown in <FIG>, in this method, first, a substrate layer <NUM> and a wire layer <NUM> are prepared.

For example, based on the method described in <CIT> and <CIT>, the substrate layer <NUM> and the wire layer <NUM> are prepared so that the wire layer <NUM> is embedded in the substrate groove <NUM>.

As shown in <FIG>, then, the pressure-sensitive adhesive layer <NUM> is disposed on the lower face of the substrate layer <NUM>.

To dispose the pressure-sensitive adhesive layer <NUM>, for example, first, an application liquid containing a material of the pressure-sensitive adhesive layer <NUM> (for example, the above-described acrylic pressure-sensitive adhesive) is prepared, and then the application liquid is applied on the upper face of the release sheet <NUM>, and thereafter, it is dried by heating. In this manner, the pressure-sensitive adhesive layer <NUM> is disposed on the upper face of the release sheet <NUM>. The release sheet <NUM> has, for example, a sheet shape extending in longitudinal direction. For the material of the release sheet <NUM>, for example, resin such as polyethylene terephthalate is used.

Then, the pressure-sensitive adhesive layer <NUM> and substrate layer <NUM> are bonded, for example, with a laminator. To be specific, the upper face of the pressure-sensitive adhesive layer <NUM> is brought into contact with the lower face of the substrate layer <NUM>.

At this point, the pressure-sensitive adhesive layer <NUM> and the substrate layer <NUM> each has no frame adhesion opening <NUM> and no frame substrate opening <NUM>, respectively.

As shown in <FIG>, then, the laminate opening <NUM> is formed in the pressure-sensitive adhesive layer <NUM> and substrate layer <NUM>.

The laminate opening <NUM> is in correspondence with the adhesion opening <NUM>, and penetrates the laminate of the pressure-sensitive adhesive layer <NUM> and substrate layer <NUM>. The laminate opening <NUM> is a hole (penetration hole) having generally a circular shape in plan view defined by an outer peripheral face defining the adhesion opening <NUM> and an outer peripheral face defined by the frame substrate opening <NUM>. That is, the laminate opening <NUM> has the same shape as that of the adhesion opening <NUM> in plan view. The laminate opening <NUM> is opened toward the upper side. Meanwhile, the lower end of the laminate opening <NUM> is closed with the release sheet <NUM>.

To form the laminate opening <NUM>, the pressure-sensitive adhesive layer <NUM> and the substrate layer <NUM> are, for example, punched or subjected to half-etching.

Thereafter, the first probe member <NUM> is prepared, and it is inserted in the laminate opening <NUM>.

As shown in <FIG>, the first probe member <NUM> has a generally rectangular shape in plan view. The first probe member <NUM> includes a probe <NUM>, a moisture barrier layer <NUM> in which the probe <NUM> is embedded, and a substrate layer <NUM> disposed on the upper face of the moisture barrier layer <NUM>.

To prepare the first probe member <NUM>, a probe-containing sheet is prepared, and the probe-containing sheet is trimmed by, for example, punching. The probe-containing sheet is prepared by, for example, producing the moisture barrier layer <NUM> and the probe <NUM> embedded in the lower face thereof, and then laminating the substrate layer <NUM> on the upper face of the moisture barrier layer <NUM>, based on the method described in <CIT><CIT>, <CIT>, <CIT>.

Thereafter, as shown in the arrow in <FIG>, the first probe member <NUM> is inserted in the laminate opening <NUM>.

At this time, a space is provided between the first probe member <NUM> and the surrounding face of the laminate opening <NUM>. That is, the first probe member <NUM> is inserted in the laminate opening <NUM> so as to form the frame substrate opening <NUM> and the frame adhesion opening <NUM>.

As shown in <FIG>, then, the connecter <NUM> is provided in the frame substrate opening <NUM> and the frame adhesion opening <NUM>.

When the material of the connecter <NUM> is electrically conductive resin, the electrically conductive resin is inserted in the frame substrate opening <NUM> and frame adhesion opening <NUM>. Thereafter, as necessary, the electrically conductive resin is heated.

The biosensor laminate <NUM> is produced in this manner.

The biosensor laminate <NUM> produced in this manner includes a pressure-sensitive adhesive layer <NUM>, moisture barrier layer <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, connecter <NUM>, and release sheet <NUM>. The biosensor laminate <NUM> may be composed only of, as shown in <FIG>, the pressure-sensitive adhesive layer <NUM>, moisture barrier layer <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, and connecter <NUM>, without including the release sheet <NUM>.

In the biosensor laminate <NUM>, when it is attached to the skin <NUM> of a living body, the moisture barrier layer <NUM> can suppress the moisture present at the interface between the skin <NUM> of a living body and the probe <NUM> to permeate through the biosensor laminate <NUM> in the thickness direction. Therefore, the moisture can be kept uniformly at the lower face of the probe <NUM>, and dryness of the probe <NUM> can be suppressed uniformly. Therefore, increase and variation in electrode impedance can be suppressed. Furthermore, fixing stability such as adherence and keeping force are excellent.

In the biosensor laminate <NUM>, the moisture barrier layer <NUM> is disposed inside the pressure-sensitive adhesive layer <NUM>. Therefore, the moisture barrier layer <NUM> is disposed at a position near the probe <NUM>. Therefore, the moisture can be kept at the lower face of the probe <NUM> even more reliably.

Furthermore, in the biosensor laminate <NUM>, the moisture barrier layer <NUM> is disposed at a side upper than the lower face of the probe. Therefore, compared with the biosensor laminate <NUM> (third embodiment, ref: <FIG>) in which the moisture barrier layer <NUM> is disposed at a lower side than the lower face of the probe <NUM>, the moisture barrier layer <NUM> does not require electrical conductivity, and the material of the moisture barrier layer <NUM> can be freely selected, and a material with high moisture barrier properties can be selected.

In the biosensor laminate <NUM>, the moisture barrier layer <NUM> includes pressure-sensitive adhesiveness. Therefore, the lower face of the moisture barrier layer <NUM> can be allowed to be exposed at the exposure region <NUM> (to be specific, gaps of the mesh) of the probe <NUM>, and the lower face of the moisture barrier layer <NUM> can be allowed to be adhered to the skin <NUM> of a living body pressure-sensitively. Therefore, the probe <NUM> can be allowed to contact the skin <NUM> of a living body uniformly and reliably, and more reliable sensing can be achieved. The moisture barrier layer <NUM> can be allowed to adhere to the connecter <NUM>, probe <NUM>, and substrate layer <NUM> pressure-sensitively, and detachment of the moisture barrier layer <NUM> can be reliably suppressed.

In the biosensor laminate <NUM>, the probe <NUM> has an exposure region <NUM> (to be specific, mesh). Thus, the moisture barrier layer <NUM> (for example, rubber resin layer) with pressure-sensitive adhesiveness can be exposed at the exposure region <NUM> (to be specific, gaps of the mesh) in the lower face of the biosensor laminate <NUM>. Thus, the entire face of the probe <NUM> can be brought into contact with the skin <NUM> of a living body. As a result, more reliable sensing can be achieved.

The biosensor laminate <NUM> is distributed singly, and is an industrially applicable device. To be specific, the biosensor laminate <NUM> can be distributed singly, separately from the electronic component <NUM> and battery <NUM> (ref: phantom line in <FIG>) to be described later. That is, in the biosensor laminate <NUM>, the electronic component <NUM> or battery <NUM> is not mounted, and it is a component for producing a biosensor such as a wearable electrocardiograph <NUM>.

Next, description is given below of a wearable electrocardiograph <NUM> as an example of a biosensor and a method for using it.

As shown in <FIG> and <FIG>, to produce a wearable electrocardiograph <NUM> including a biosensor laminate <NUM>, for example, first, the biosensor laminate <NUM>, electronic component <NUM>, and battery <NUM> are prepared.

Examples of the electronic component <NUM> include an analog front-end, microcomputer, and memory for processing and storing electric signals from a living body obtained by the probe <NUM>; and a communication IC and transmitter for converting electric signals to electro-magnetic waves and wirelessly transmitting them to an external receiver. The electronic component <NUM> may include some or all of these. The electronic component <NUM> has two, or three or more terminals (not shown) provided on the lower face thereof.

The battery <NUM> has two terminals (not shown) provided at its lower face.

Then, the two terminals of the electronic component <NUM> are electrically connected with the first terminal 17A and third terminal 17C. The two terminals of the battery <NUM> are electrically connected with the second terminal 17B and fourth terminal 17D.

In this manner, the wearable electrocardiograph <NUM> including the biosensor laminate <NUM>, the electronic component <NUM> and the battery <NUM> is produced, where the electronic component <NUM> and the battery <NUM> are mounted on the biosensor laminate <NUM>.

To use the wearable electrocardiograph <NUM>, first, the release sheet <NUM> (ref: arrow and phantom line in <FIG>) is released from the pressure-sensitive adhesive layer <NUM> and probe <NUM>.

As shown with the phantom line in <FIG>, then, the lower face of the pressure-sensitive adhesive layer <NUM> is brought into contact with, for example, the skin <NUM> of a living body. To be specific, the pressure-sensitive adhesive layer <NUM> is brought into contact with (attached to) the skin <NUM> puressure-sensitivly. In this manner, the lower face of the probe <NUM> is brought into contact with the surface of the skin <NUM>.

At this time, the lower face of the probe <NUM>, or the surface of the skin <NUM> is wetted with water. In this manner, water is inserted at the interface between the lower face of the probe <NUM> and skin <NUM>.

Then, the probe <NUM> senses the cardiac action potential as electric signals, and the electric signal sensed acquired by the probe <NUM> is inputted to the electronic component <NUM> through the connecter <NUM> and wire layer <NUM>. The electronic component <NUM> processes the electric signal based on the electric power supplied from the battery <NUM>, and store that information. Furthermore, as necessary, the electric signals are converted to electro-magnetic waves, and they are wirelessly transmitted to an external receiver.

In the method of using the wearable electrocardiograph <NUM>, the impedance of the probe <NUM> can be decreased because water which increases electrical conductivity is provided at the interface between the probe <NUM> and skin <NUM>. Thus, sensing of noise, i.e., other than the cardiac electric signal, can be suppressed.

In the method of using the wearable electrocardiograph <NUM>, the wearable electrocardiograph <NUM> includes the biosensor laminate <NUM>, and therefore the moisture barrier layer <NUM> is present in the thickness direction of the probe <NUM>. Thus, the moisture permeation through the biosensor is suppressed, and the drying of the interface is suppressed. Thus, even when it is attached to a living body and used for a long period of time, increase in the impedance of the probe <NUM> can be suppressed. Furthermore, sufficient water can be present uniformly at the interface, and therefore variation in impedance of the probe <NUM> can also be suppressed.

In the modified examples below, the members and steps corresponding to those described in the embodiment above are designated by the same reference numerals, and detailed descriptions thereof are omitted. These modified examples can be suitably combined. Furthermore, the modified examples have the same operations and effects as those in the embodiment unless otherwise noted.

In the embodiment shown in <FIG>, the contour of the moisture barrier layer <NUM> coincides with the contour of the probe <NUM> when projected in the thickness direction, but for example, as shown in <FIG>, the moisture barrier layer <NUM> may include the probe <NUM> when projected in the thickness direction. That is, the contour of the moisture barrier layer <NUM> may be larger than the contour of the probe <NUM> in plan view.

In the embodiment shown in <FIG>, the moisture barrier layer <NUM> includes an inner barrier layer 3a disposed inside the connecter <NUM>, and an outer barrier layer 3b disposed outside the connecter <NUM>.

The inner barrier layer 3a has a generally rectangular shape in plan view, and its external peripheral face is in contact with the inner periphery of the connecter <NUM>.

The outer barrier layer 3b has a generally rectangular frame shape in plan view, and its inner peripheral face is in contact with the external peripheral face of the connecter <NUM>, and its external peripheral face is in contact with the pressure-sensitive adhesive layer <NUM>.

The barrier region <NUM> is larger than the probe region <NUM>. To be specific, the ratio of the area A1 of the barrier region <NUM> relative to the area A3 of the probe region <NUM> (A1/A3) is, for example, more than <NUM>, preferably <NUM> or more, more preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less. To be specific, the area A1 of the barrier region <NUM> is, for example, <NUM><NUM> or more, preferably <NUM><NUM> or more, and for example, <NUM><NUM> or less, preferably <NUM><NUM> or less. When the area A1 of the barrier region <NUM> is the above-described lower limit or more, increase and variation in impedance of the probe <NUM> can be suppressed even more. When the area A1 of the barrier region <NUM> is the above-described upper limit or less, wearability can be improved even more.

In view of excellent wearability, preferably, the embodiment as shown in <FIG> is used. Meanwhile, in view of suppressing increase and variation in probe impedance even more, preferably, the embodiment shown in <FIG> is used.

As shown in <FIG>, in the embodiment shown in <FIG>, the contour of the moisture barrier layer <NUM> coincides with the contour of the probe <NUM> when projected in the thickness direction, but for example, the moisture barrier layer <NUM> may be included in the probe <NUM> when projected in the thickness direction. That is, the contour of the moisture barrier layer <NUM> may be smaller than the contour of the probe <NUM> in plan view, and the above-described ratio (A1/A3) is less than <NUM>.

In view of reliably suppressing the moisture permeation at the entire probe <NUM> in plan view and suppressing increase and variation in impedance, preferably, the embodiment shown in <FIG> and <FIG> is used.

In the embodiment shown in <FIG>, the probe <NUM> has a mesh shape in plan view including an exposure region <NUM>, but for example, although not shown, the probe <NUM> may have a shape having no exposure region <NUM> (for example, a generally rectangular shape in plan view).

Preferably, the embodiment shown in <FIG> is used. In the embodiment shown in <FIG>, the lower face of the moisture barrier layer <NUM> having pressure-sensitive adhesiveness, where the lower face is exposed at the exposure region <NUM> of the probe <NUM>, makes contact with the skin <NUM> of a living body. Thus, the probe <NUM> can be brought into contact with the skin <NUM> of a living body uniformly and reliably, and more accurate sensing can be performed.

In the embodiment shown in <FIG>, the contour of the probe <NUM> has a generally rectangular shape in plan view and the connecter <NUM> has a generally rectangular frame shape in plan view, but for example, as shown in <FIG>, the contour of the probe <NUM> may have a generally circular shape in plan view, and the connecter <NUM> may have a generally ring shape in plan view.

In the embodiment shown in <FIG>, the substrate layer <NUM> is disposed on the upper face of the moisture barrier layer <NUM>, but for example, as shown in <FIG>, the pressure-sensitive adhesive layer <NUM> may be interposed between the moisture barrier layer <NUM> and substrate layer <NUM>. That is, in the embodiment shown in <FIG>, the moisture barrier layer <NUM>, the pressure-sensitive adhesive layer <NUM> disposed on the upper face of the moisture barrier layer <NUM>, and the substrate layer <NUM> disposed on the upper face of the pressure-sensitive adhesive layer <NUM> are included inside the connecter <NUM>.

In the embodiment shown in <FIG> and <FIG>, the wearable electrocardiograph <NUM> is given as an example of the biosensor of the present invention, but for example, those devices that can perform sensing of signals from a living body to monitor health conditions of a living body are included. Examples of devices include a wearable electroencephalograph, wearable sphygmomanometer, wearable pulse meter, wearable electromyograph, and wearable thermometer. The living body includes a human body and animals other than human, but preferably, human body.

The second embodiment of the laminate for biosensor of the present invention is described with reference to <FIG>. In the second embodiment, those members and steps that are the same as the above-described first embodiment are designated by the same reference numerals, and detailed descriptions thereof are omitted. In the second embodiment, those members and steps that are the same as the above-described first embodiment have the same configuration (shape, material, physical property, etc.) and operations and effects as those in the embodiment unless otherwise noted.

As shown in <FIG>, the biosensor laminate <NUM> as a second embodiment includes a pressure-sensitive adhesive layer (first pressure-sensitive adhesive layer) <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, connecter <NUM>, second pressure-sensitive adhesive layer <NUM>, and moisture barrier layer <NUM>. To be specific, the biosensor laminate <NUM> includes a first pressure-sensitive adhesive layer <NUM>, substrate layer <NUM> disposed on the upper face of the first pressure-sensitive adhesive layer <NUM>, wire layer <NUM> embedded in the substrate layer <NUM>, probe <NUM> embedded in the pressure-sensitive adhesive layer <NUM>, connecter <NUM> that electrically connects the wire layer <NUM> and probe <NUM>, second pressure-sensitive adhesive layer <NUM> disposed on the upper face of the substrate layer <NUM>, and moisture barrier layer <NUM> disposed on the upper face of the second pressure-sensitive adhesive layer <NUM>.

As shown in <FIG>, the first pressure-sensitive adhesive layer <NUM> forms the lower face of the biosensor laminate <NUM>. The first pressure-sensitive adhesive layer <NUM> forms the contour of the biosensor laminate <NUM>.

The first pressure-sensitive adhesive layer <NUM> has a frame adhesion opening <NUM> at both end portions in longitudinal direction thereof. The first pressure-sensitive adhesive layer <NUM> also has a pressure-sensitive adhesive layer (pressure-sensitive adhesive layer <NUM> for probe) having a generally rectangular shape in plan view inside the frame adhesion opening <NUM>. The frame adhesion opening <NUM> is filled with the connecter <NUM>. The lower face of the pressure-sensitive adhesive layer (pressure-sensitive adhesive layer <NUM> for probe) inside the frame adhesion opening <NUM> has an adhesion groove <NUM> corresponding to the probe <NUM>.

As shown in <FIG>, the substrate layer <NUM> forms the upper face of the biosensor laminate <NUM>. The substrate layer <NUM> forms the contour of the biosensor laminate <NUM> along with the pressure-sensitive adhesive layer <NUM>. The shape of the substrate layer <NUM> in plan view is the same as the shape of the pressure-sensitive adhesive layer <NUM> in plan view.

The wire layer <NUM> is embedded in the substrate groove <NUM>, as shown in <FIG>.

The probe <NUM> is embedded in the adhesion groove <NUM> of the first pressure-sensitive adhesive layer <NUM>, as shown in <FIG>. To be specific, the probe <NUM> is embedded at a lower end portion of the pressure-sensitive adhesive layer <NUM> for probe inside the connecter <NUM>.

The connecter <NUM> is provided, as shown in <FIG>, in correspondence with the frame substrate opening <NUM> and frame adhesion opening <NUM>, and has the same shape as those.

The internal face of the connecter <NUM> is in contact with the probe <NUM>, pressure-sensitive adhesive layer <NUM>, and substrate layer <NUM>; and the external face of the connecter <NUM> is in contact with the pressure-sensitive adhesive layer <NUM>, and substrate layer <NUM>.

The second pressure-sensitive adhesive layer <NUM> is a layer for adhesively bonding the substrate layer <NUM> and the moisture barrier layer <NUM>.

The second pressure-sensitive adhesive layer <NUM> is disposed at a portion of the upper face of the substrate layer <NUM>, as shown in <FIG>. The second pressure-sensitive adhesive layer <NUM> is disposed so as to overlap with the probe <NUM> when projected in the thickness direction. To be specific, it is disposed so that the contour of the second pressure-sensitive adhesive layer <NUM> coincides with the contour of the probe <NUM> (also inner shape of the connecter <NUM>) when projected in the thickness direction. That is, the contour of the second pressure-sensitive adhesive layer <NUM> is the same as that of the contour of the probe <NUM> in plan view.

For the material of the second pressure-sensitive adhesive layer <NUM>, a material having pressure-sensitive adhesiveness is used, and for example, the material for the first pressure-sensitive adhesive layer <NUM> can be used, and preferably, acrylic pressure-sensitive adhesives are used.

The second pressure-sensitive adhesive layer <NUM> has a moisture permeability of, for example, <NUM>/m<NUM>·day or more, preferably <NUM>/m<NUM>·day or more, and for example, <NUM>/m<NUM>·day or less.

The second pressure-sensitive adhesive layer <NUM> has a thickness of, for example, <NUM> or more, preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less, more preferably <NUM> or less.

The moisture barrier layer <NUM> forms a portion of the upper face of the biosensor laminate <NUM>, as shown in <FIG>. The moisture barrier layer <NUM> is disposed on the entire upper face of the second pressure-sensitive adhesive layer <NUM>. The shape of the moisture barrier layer <NUM> in plan view is the same as the shape of the second pressure-sensitive adhesive layer <NUM> in plan view. That is, the contour of the moisture barrier layer <NUM> is the same as the contour of the probe <NUM> in plan view.

Examples of the moisture barrier layer <NUM> include examples described above regarding the moisture barrier layer <NUM> described in the first embodiment.

The upper face of the moisture barrier layer <NUM> preferably has no pressure-sensitive adhesiveness in view of handleability. Examples of the moisture barrier layer include, preferably, a polyolefin resin layer, acrylic resin layer, and polyvinyl resin layer; more preferably, polyolefin resin layer and acrylic resin layer; and even more preferably, polyolefin resin layer.

The moisture permeability of the moisture barrier layer <NUM> is the same as that of the first embodiment. Area A1 of the barrier region <NUM> is generally the same as area A3 of the probe region <NUM>, as in the first embodiment.

The moisture barrier layer <NUM> has a thickness of, for example, <NUM> or more, preferably <NUM> or more, and for example, <NUM> or less, preferably <NUM> or less.

Next, description is given below of the method for producing a biosensor laminate <NUM> in an embodiment with reference to <FIG>.

In this method, in the same manner as in the first embodiment, first, the substrate layer <NUM> and wire layer <NUM> are prepared (ref: <FIG>, <FIG>), and then the pressure-sensitive adhesive layer <NUM> is disposed on the lower face of the substrate layer <NUM> (ref: <FIG>, <FIG>).

Then, the laminate opening <NUM> is formed on the pressure-sensitive adhesive layer <NUM> and substrate layer <NUM> (ref: <FIG>, <FIG>).

Thereafter, a second probe member <NUM> is prepared, and inserted into the laminate opening <NUM>.

As shown in <FIG>, the second probe member <NUM> includes a probe <NUM>, a first pressure-sensitive adhesive layer <NUM> in which the probe <NUM> is embedded, and a substrate layer <NUM> disposed on the upper face of the first pressure-sensitive adhesive layer <NUM>. Preparation of the second probe member <NUM> is conducted in the same manner as in the preparation of the first probe member <NUM>, except that the material of the moisture barrier layer <NUM> is changed to the material of the first pressure-sensitive adhesive layer <NUM>.

As shown in <FIG>, then, the connecter <NUM> is provided inside the frame substrate opening <NUM> and frame adhesion opening <NUM>.

As shown in <FIG>, then, the second pressure-sensitive adhesive layer <NUM> and moisture barrier layer <NUM> are disposed in this order on the upper face of the substrate layer <NUM>.

First, the second pressure-sensitive adhesive layer <NUM> is disposed on a release sheet, and the second pressure-sensitive adhesive layer <NUM> is bonded to the substrate layer <NUM>, and thereafter, the release sheet is removed from the second pressure-sensitive adhesive layer <NUM>. This is conducted in the same manner as in the method of disposing the pressure-sensitive adhesive layer <NUM> on the substrate layer <NUM> in the first embodiment.

Then, the moisture barrier layer <NUM> is bonded to the second pressure-sensitive adhesive layer <NUM> by, for example, lamination. To be specific, the lower face of the moisture barrier layer <NUM> is brought into contact with the upper face of the second pressure-sensitive adhesive layer <NUM>.

The lower face of the second pressure-sensitive adhesive layer <NUM> may be bonded to the upper face of the substrate layer <NUM> after the upper face of the second pressure-sensitive adhesive layer <NUM> is bonded to the moisture barrier layer <NUM>.

The thus produced biosensor laminate <NUM> includes a release sheet <NUM>, first pressure-sensitive adhesive layer <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, connecter <NUM>, second pressure-sensitive adhesive layer <NUM>, and moisture barrier layer <NUM>. The biosensor laminate <NUM> may be composed of the first pressure-sensitive adhesive layer <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, connecter <NUM>, second pressure-sensitive adhesive layer <NUM>, and moisture barrier layer <NUM> without including the release sheet <NUM>, as shown in <FIG>,.

The biosensor laminate <NUM> of the second embodiment achieves the same operations and effects as those of the biosensor laminate <NUM> in the first embodiment. Preferably, in view of suppressing increase and variation in impedance even more, and in view of even more excellent wearability, laminate for biosensor in the first embodiment is used.

In the biosensor laminate <NUM>, the moisture barrier layer <NUM> is disposed at the upper side of the substrate layer <NUM>. Therefore, the moisture barrier layer <NUM> can be disposed easily on the upper side of the substrate layer <NUM> through the second pressure-sensitive adhesive layer <NUM>. Therefore, production suitability is excellent.

The biosensor laminate <NUM> in the second embodiment may be used, for example, a wearable electrocardiograph <NUM> as an example of the biosensor. The wearable electrocardiograph <NUM>, in which the biosensor laminate <NUM> of the second embodiment is used, the method of using it and operations and effects are the same as the wearable electrocardiograph <NUM>, in which the biosensor laminate <NUM> in the first embodiment is used, the method of using it and Operations and effects.

In the embodiment shown in <FIG>, the contour of the moisture barrier layer <NUM> coincides with the contour of the probe <NUM> when projected in the thickness direction, but for example, as shown in <FIG>, the moisture barrier layer <NUM> can include the probe <NUM> when projected in the thickness direction. That is, the contour of the moisture barrier layer <NUM> can be larger than the contour of the probe <NUM> in plan view.

At this time, the second pressure-sensitive adhesive layer <NUM> also has the same shape and size as those of the moisture barrier layer <NUM>.

Area A1 of the barrier region <NUM> is larger than area A3 of the probe region <NUM>, to be specific, it is the same as in the first modified example of the first embodiment.

In view of excellent wearability, preferably, the embodiment shown in <FIG> is used. Meanwhile, in view of suppressing increase and variation in impedance even more, preferably, the embodiment shown in <FIG> is used.

In the embodiment shown in <FIG>, as shown in <FIG>, the contour of the moisture barrier layer <NUM> coincides with the contour of the probe <NUM> when projected in the thickness direction, but for example, the moisture barrier layer <NUM> can be included in the probe <NUM> when projected in the thickness direction. That is, the contour of the moisture barrier layer <NUM> can be smaller than the contour of the probe <NUM> in plan view.

In view of reliably suppressing permeation of moisture in the entirety of the probe <NUM> in plan view, and increase and variation in impedance, preferably, the embodiment shown in <FIG> and <FIG> is used.

The third modified example, fourth modified example, and sixth modified example of the first embodiment can also be applied to a modified example of the second embodiment, and their operations and effects are the same.

A third embodiment of the laminate for biosensor of the present invention is described with reference to <FIG>. In the second embodiment, those members and steps that are the same as those in the above-described first embodiment are designated by the same reference numerals, and detailed descriptions thereof are omitted. In the third embodiment, those members and steps that are the same as the above-described first embodiment have the same configuration (shape, material, physical property, etc.) and operations and effects as those in the first embodiment unless otherwise noted.

As shown in <FIG>, the biosensor laminate <NUM> in third embodiment includes a pressure-sensitive adhesive layer (first pressure-sensitive adhesive layer) <NUM>, substrate layer <NUM>, wire layer <NUM>, probe <NUM>, connecter <NUM>, and moisture barrier layer <NUM>. To be specific, the biosensor laminate <NUM> includes a first pressure-sensitive adhesive layer <NUM>, substrate layer <NUM> disposed on the upper face of the first pressure-sensitive adhesive layer <NUM>, wire layer <NUM> embedded in the substrate layer <NUM>, probe <NUM> embedded in the pressure-sensitive adhesive layer <NUM>, connecter <NUM> that electrically connects the wire layer <NUM> and the probe <NUM>, and moisture barrier layer <NUM> disposed on the lower face of the probe <NUM> and pressure-sensitive adhesive layer <NUM>.

The moisture barrier layer <NUM> in the third embodiment has electrical conductivity. In this manner, water can be kept at the interface between the skin of a living body <NUM> and the moisture barrier layer <NUM>, while allowing conductivity with the probe <NUM>.

For the material of the electrically conductive moisture barrier layer <NUM>, an electrically conductive particle-containing composition in which known electrically conductive particles are blended to a rubber composition such as the above-described polyisobutylene composition is used.

The contour of the moisture barrier layer <NUM> coincides with the contour of the probe <NUM> when projected in the thickness direction.

Preferably, the biosensor laminate <NUM> of the first embodiment and second embodiment is used. With the biosensor laminate <NUM>, electrically conductive particles are not necessary for the material of the moisture barrier layer <NUM>, and materials for the moisture barrier layer can be selected freely. As a result, a material with high moisture barrier properties can be selected. Furthermore, the lower face of the biosensor laminate <NUM> can be made flat entirely, and therefore it can be attached to a living body excellently.

The first to fourth modified examples and sixth modified example of the first embodiment can also be applied to the third embodiment as modified examples, and their operations and effects are the same.

Hereinafter, the present invention is described in further detail with reference to Examples and Comparative Examples. However, the present invention is not limited to those described in Examples and Comparative Examples. The specific numerical values of mixing ratio (content), physical property value, and parameter used in the description below can be replaced with the upper limit values (numerical values defined with "or less" or "below") or lower limit values (numerical values defined with "or more" or "more than") of the corresponding numerical values of mixing ratio (content), physical property value, and parameter described in "DESCRIPTION OF EMBODIMENTS" above.

To conduct the test shown in <FIG>, an impedance measurement sample 50a shown in <FIG> is prepared.

To be specific, first, a polyethylene terephthalate (PET) film (<NUM> × <NUM>) was prepared as the release sheet <NUM>.

An application liquid of the electrical conductive resin composition was prepared by mixing <NUM> of <NUM>% aqueous solution of electrical conductive polymer ("Clevious PH <NUM>", containing PEDOT-PSS, manufactured by Heraeus), <NUM> of <NUM>% aqueous solution modified polyvinyl alcohol ("Gohsenol Z410", manufactured by The Nippon Synthetic Chemical Industry Co. ), <NUM> of <NUM>% aqueous solution of zirconium cross-linking agent ("Safelink SPM-<NUM>", manufactured by Mitsubishi Chemical Corporation), <NUM> of glycerine (plasticizer, manufactured by Wako Pure Chemical Industries, Ltd. ), and <NUM> of silicone surfactant ("SILFACE SA503A", manufactured by Nissin Chemical Industry Co. The application liquid was applied on the upper face of the PET film so that a probe <NUM> having a grid shape in plan view (length <NUM> × width <NUM>, thickness <NUM>) and projected connecter <NUM> were formed, and then cured by heating. In this manner, a probe sheet <NUM> was produced (ref: <FIG>).

Then, <NUM> parts by mass of polyisobutylene (<NUM> mass% of "OPPANOL N80", manufactured by BASF, <NUM> mass% of "Tetrax 5T", manufactured by JXTG energy), <NUM> parts by mass of liquid polybutene ("HV-<NUM>", manufactured by JXTG energy), <NUM> parts by mass of crosslinked sodium salt of isobutylene-maleic anhydride copolymer ("KI gel", manufactured by Kuraray Trading Co. ), <NUM> parts by mass of petroleum resin ("EscorezTM 1202U", manufactured by EMG Marketing G. ), <NUM> parts by mass of hexamethylene diisocyanate ("BASONAT HA2000", manufactured by BASF), and <NUM> parts by mass of calcium carbonate heavy (manufactured by Maruo calcium Co. ) were diluted with toluene solvent, thereby preparing a polyisobutylene composition solution. The polyisobutylene composition solution was applied to a second release sheet (PET film), and dried by heating. A moisture barrier layer sheet including the pressure-sensitive adhesiveness was produced in this manner. The moisture barrier layer <NUM> had a generally rectangular shape in plan view (<NUM> × <NUM>, thickness <NUM>).

Then, the moisture barrier layer sheet was disposed on the probe sheet <NUM> so that the probe <NUM> was embedded in the moisture barrier layer <NUM>, and the second release sheet was released from the moisture barrier layer <NUM>. At this time, the moisture barrier layer <NUM> was disposed so that the contour of the probe <NUM> coincided with the contour of the moisture barrier layer <NUM>. In this manner, a first laminate <NUM> including the moisture barrier layer <NUM>, probe sheet <NUM>, and release sheet <NUM> is produced (ref: <FIG>).

Then, <NUM> parts by mass of acrylic acid isononyl, <NUM> parts by mass of acrylic acid methoxy ethyl, and <NUM> parts by mass of acrylic acid were copolymerized to prepare acrylic polymer. Then, <NUM> parts by mass of the acrylic polymer, <NUM> parts by mass of capric triglyceride (trade name "COCONARD", manufactured by Kao Corporation), and <NUM> parts by mass of polyfunctional isocyanate (trade name "CORONATER HL", manufactured by Nippon Polyurethane Industry Co. ) were stirred and mixed, thereby preparing an acrylic pressure-sensitive adhesive composition. Then, the acrylic pressure-sensitive adhesive composition was applied on the upper face of the third release sheet (PET film), and then dried by heating. The pressure-sensitive adhesive layer sheet was produced in this manner. The pressure-sensitive adhesive layer <NUM> had a generally rectangular shape in plan view (<NUM> × <NUM>, thickness <NUM>).

Then, the pressure-sensitive adhesive layer sheet was disposed on the first laminate <NUM> so that the moisture barrier layer <NUM> is embedded in the pressure-sensitive adhesive layer <NUM>, and the third release sheet was released from the moisture barrier layer <NUM>. At this time, the pressure-sensitive adhesive layer <NUM> was disposed so that the center of the contour of the probe <NUM> coincide with the center of the contour of the pressure-sensitive adhesive layer <NUM>. In this manner, the second laminate <NUM> including a pressure-sensitive adhesive layer <NUM>, moisture barrier layer <NUM>, probe <NUM>, and release sheet <NUM> was produced (ref: <FIG>. In the second laminate <NUM>, the thickness of the moisture barrier layer <NUM> is substantially the same as that of the moisture barrier layer <NUM> before lamination, and the pressure-sensitive adhesive layer <NUM> disposed on the upper face of the moisture barrier layer <NUM> had a thickness of about less than about <NUM>.

Then, the polyurethane-containing solution (trade name "PANDEX T-8180N", manufactured by DIC Covestro Polymer Ltd. ) was stirred and mixed with capric triglyceride ("trade name COCONARD", manufactured by Kao Corporation) so that the mass ratio (solid content) of "polyurethane : capric triglyceride" was <NUM> :<NUM>, thereby preparing a substrate composition solution. The substrate composition solution was applied on the upper face of the fourth release sheet, and then dried by heating. The substrate layer sheet was produced in this manner. The substrate layer <NUM> had a size of <NUM> × <NUM> and a thickness of <NUM>.

Then, the substrate layer sheet was disposed on the second laminate so that the substrate layer <NUM> was allowed to contact the pressure-sensitive adhesive layer <NUM> pressure-sensitively, and the fourth release sheet was released from the pressure-sensitive adhesive layer <NUM>.

In this manner, the measurement sample 50a of Example <NUM> including the pressure-sensitive adhesive layer <NUM>, moisture barrier layer <NUM>, probe <NUM>, and release sheet <NUM> was produced (ref: <FIG>.

The measurement sample 50a was produced in the same manner as in Example <NUM>, except that the moisture barrier layer <NUM> had a generally rectangular shape in plan view with <NUM> × <NUM> (ref: <FIG>.

The measurement sample 50a was produced in the same manner as in Example <NUM>, except that the moisture barrier layer <NUM> had a generally rectangular shape in plan view of <NUM> × <NUM>, and the pressure-sensitive adhesive layer <NUM> was not used (ref: <FIG>.

The measurement sample 50a was produced in the same manner as in Example <NUM>, except that a natural rubber-SBR mixed resin layer (product "drape tape", manufactured by Nitto Denko Corporation) was used as the moisture barrier layer <NUM>, and the thickness was set to <NUM> (ref: <FIG>.

The measurement sample 50a was produced in the same manner as in Example <NUM>, except that a SBR resin layer (product "SLY-<NUM>", manufactured by Nitto Denko Corporation) was used as the moisture barrier layer <NUM>, and the thickness was set to <NUM> (ref: <FIG>.

The impedance measurement sample 50b shown in <FIG> was produced.

To be specific, first, a probe sheet <NUM> of Example <NUM> was prepared (ref: <FIG>.

The pressure-sensitive adhesive layer sheet of Example <NUM> (first pressure-sensitive adhesive layer : <NUM> × <NUM>, thickness <NUM>) was prepared. The pressure-sensitive adhesive layer sheet was disposed on the probe sheet <NUM> so that the probe <NUM> was embedded in the pressure-sensitive adhesive layer <NUM>, and the second release sheet was released from the probe <NUM>. In this manner, a second-first laminate <NUM> including the release sheet <NUM>, probe <NUM>, and first pressure-sensitive adhesive layer <NUM> was produced (ref: <FIG>.

The substrate layer sheet of Example <NUM> (substrate layer <NUM> × <NUM>, thickness <NUM>) was prepared. The substrate layer sheet was disposed on the second-first laminate <NUM> so that the substrate layer <NUM> was in contact with the pressure-sensitive adhesive layer <NUM> pressure-sensitively, and the fourth release sheet was released from the pressure-sensitive adhesive layer <NUM>. In this manner, the second-second laminate <NUM> including the substrate layer <NUM>, first pressure-sensitive adhesive layer <NUM>, probe <NUM>, and release sheet <NUM> was produced (ref: <FIG>.

The pressure-sensitive adhesive layer sheet of Example <NUM> (second pressure-sensitive adhesive layer <NUM>: thickness <NUM>) was prepared, except that the size was changed to <NUM> × <NUM>.

The pressure-sensitive adhesive layer sheet was disposed on the second-second laminate <NUM> so that the probe <NUM> and the pressure-sensitive adhesive layer coincide with each other in plan view, and the pressure-sensitive adhesive layer <NUM> is in contact with the substrate layer <NUM> pressure-sensitively; and the second release sheet was released from the pressure-sensitive adhesive layer <NUM>. Then, a moisture barrier layer <NUM> (polyolefin resin layer, <NUM> × <NUM>, thickness <NUM>, "No. <NUM>", manufactured by Nitto) was disposed on the entire face of the second pressure-sensitive adhesive layer <NUM>.

In this manner, the measurement sample 50b of Example <NUM> including the moisture barrier layer <NUM>, second pressure-sensitive adhesive layer <NUM>, substrate layer <NUM>, first pressure-sensitive adhesive layer <NUM>, probe <NUM>, and release sheet <NUM> was produced (ref: <FIG>.

The measurement sample 50b was produced in the same manner as in Example <NUM>, except that the size of the moisture barrier layer <NUM> and second pressure-sensitive adhesive layer <NUM> were changed to <NUM> × <NUM> (ref: <FIG>).

The measurement sample 50b was produced in the same manner as in Example <NUM> (ref: <FIG>), except that in the moisture barrier layer <NUM>, the polyolefin resin layer was changed to an acrylic resin layer (acrylic foam, <NUM> × <NUM>, thickness <NUM>, "ISR-ACF-510AD", manufactured by Iwatani Corporation).

The measurement sample 50b was produced in the same manner as in Example <NUM> (ref: <FIG>), except that in the moisture barrier layer <NUM>, the polyolefin resin layer was changed to a poly propylene resin layer (poly propylene foam, <NUM> × <NUM>, thickness <NUM>, "SCF-<NUM>", manufactured by Nitto).

The measurement sample 50b was produced in the same manner as in Example <NUM> (ref: <FIG>), except that in the moisture barrier layer <NUM>, the polyolefin resin layer was changed to a poly vinyl alcohol resin layer (<NUM> × <NUM>, thickness <NUM>).

The poly vinyl alcohol resin layer was produced by drying the <NUM>% aqueous solution of poly vinyl alcohol ("Gohsenol Z410") manufactured by Nippon Synthetic Chemical Industry Co.

The measurement sample 50b was produced in the same manner as in Example <NUM> (ref: <FIG>), except that in the moisture barrier layer <NUM>, the polyolefin resin layer was changed to the moisture barrier layer (polyisobutylene resin layer, <NUM> × <NUM>, thickness <NUM>) produced in Example <NUM>.

A measurement sample (a laminate of substrate layer <NUM>, first pressure-sensitive adhesive layer <NUM>, probe <NUM>, and release sheet <NUM>) was produced in the same manner as in Example <NUM>, except that the measurement sample had no second pressure-sensitive adhesive layer <NUM> and no moisture barrier layer <NUM> disposed therein.

The moisture permeability of the moisture barrier layer, pressure-sensitive adhesive layer, and substrate layer was measured based on the following procedure (ref: <FIG>).

The substrate layer (thickness <NUM>) used in Examples and Comparative Examples had a moisture permeability of <NUM>/m<NUM>·day, and the pressure-sensitive adhesive layer (thickness <NUM>) had a moisture permeability of <NUM>/m<NUM>·day. The moisture permeability of the moisture barrier layer is shown in Table <NUM>.

A pair of measurement samples (50a, 50b) was prepared for Examples and Comparative Examples. The release sheet <NUM> was released from the sample, and then each of the connecters <NUM> of the pair of the measurement samples was electrically connected to an impedance analyzer <NUM> through a lead <NUM>, and the measurement sample was attached to a pig skin <NUM> (Yucatan Micropig Skinset). Upon attaching, physiological saline was dropped between the pig skin <NUM> and measurement sample (50a, 50b) to allow the probe <NUM> in initial state to be wet. The test scheme is shown in <FIG>.

The impedance (frequency <NUM>) between the measurement samples was measured after <NUM> hours, <NUM> hour, <NUM> hours, <NUM> hours, <NUM> hours, <NUM> hours, and <NUM> hours. For the impedance analyzer <NUM>, "IM3540" (trade name) manufactured by HIOKI was used.

Table <NUM> shows the results thereof, the maximum impedance, and variation (difference of the maximum value and the minimum value of the measured impedance).

The release sheet was removed from the sample of Examples and Comparative Examples, and attached to a human skin. The wearability was evaluated as follows.

The moisture barrier layer sheet (length <NUM> × width <NUM> × thickness <NUM>) of Examples and the first pressure-sensitive adhesive layer (length <NUM> × width <NUM> × thickness <NUM>) of Comparative Examples were prepared, and laminated on the entire face of a PET film (length <NUM> × width <NUM> × thickness <NUM>) to prepare samples.

The sample was allowed to contact a bakelite plate, and then a <NUM> weight was allowed to go back and forth on the sample surface to be attached. After <NUM> minutes after the attachment, the sample was peeled under the conditions of <NUM>° peel and a tensile speed of <NUM>/min with a peel testing machine to measure peeling force (tensile tester, "AG-<NUM>"). The measurement was conducted three times, and the average value is shown in Table <NUM>.

The peeling force was measured in the same manner as described above, except that human skin was used instead of the bakelite plate. The results are shown in Table <NUM>.

The moisture barrier layer sheet of Examples (length <NUM> × width <NUM> × thickness <NUM>) and the first pressure-sensitive adhesive layer (length <NUM> × width <NUM> × thickness <NUM>) of Comparative Examples were prepared, and laminated on the entire face of a PET film (length <NUM> × width <NUM> × thickness <NUM>) to prepare a sample.

The sample was brought into contact with the Bakelite plate, and a <NUM> weight was allowed to go back and forth to be attached. After <NUM> minutes after the attachment, a <NUM> weight was put on the sample, and then the sample and Bakelite plate were put on the wall so that its longitudinal direction coincides with the vertical direction. At this time, the time when the sample fell off from the bakelite plate was measured. The results are shown in Table <NUM>.

When the peeling force relative to human skin was more than <NUM> N/<NUM>, and the keeping force was more than <NUM> minutes, it was evaluated as "Excellent. " When the peeling force relative to human skin was more than <NUM>. N/ <NUM>, and keeping force was <NUM> minutes or less, it was evaluated as "Good. " When the peeling force relative to human skin was <NUM> N/ <NUM> or less, and keeping force was <NUM> minutes or less, it was evaluated as "Fair. " The results are shown in Table <NUM>.

While the illustrative embodiments of the present invention are provided in the above description, such is for illustrative purpose only and it is not to be construed as limiting in any manner.

The invention is as defined in the appended claim.

Claim 1:
A laminate for biosensor (<NUM>) comprising:
a pressure-sensitive adhesive layer (<NUM>) for attaching to a living body; and
a substrate layer (<NUM>) disposed on the upper face of the pressure-sensitive adhesive layer,
wherein the laminate for biosensor includes
a moisture barrier layer (<NUM>) disposed inside the pressure-sensitive adhesive layer and having an exposed lower face, and
a probe (<NUM>) embedded in the moisture barrier layer and having a lower face exposed from the lower face of the moisture barrier layer.