JP2020156872A - Sticking type biological sensor - Google Patents

Abstract

To provide a sticking type biological sensor that is suitable for a disposable type.SOLUTION: A sticking type biological sensor includes: a pressure-sensitive adhesion layer having a sticking surface to be stuck on an analyte; an electrode to be brought into contact with the analyte; a base material layer provided so as to be superposed on the opposite surface to the sticking surface of the pressure-sensitive adhesion layer; an electronic device that is provided on the base material layer, includes an integrated circuit and an information processor, and processes analogue data acquired through the electrode; and a circuit unit that is provided on the base material layer and connects the electrode to the electronic device. The integrated circuit includes: a first input terminal connected to the electrode; an A/D converter for converting analogue data input through the first input terminal to digital data; and an output terminal. The information processor includes a second input terminal connected to the output terminal. The integrated circuit includes a control unit for outputting the digital data from the output terminal to the information processor.SELECTED DRAWING: Figure 1

Description

The present invention relates to a stick-on biosensor.

Conventionally, there is a biosensor using a biocompatible polymer substrate including a plate-shaped first polymer layer, a plate-shaped second polymer layer, an electrode, and a data acquisition module (see, for example, Patent Document 1). ).

Japanese Unexamined Patent Publication No. 2012-010978

By the way, in order to make the biosensor a disposable type, one issue is whether or not it can be manufactured at low cost.

Therefore, it is an object of the present invention to provide a stick-on biosensor suitable for a disposable type.

The stick-on biosensor according to the embodiment of the present invention has a pressure-sensitive adhesive layer having a sticking surface to be stuck to a subject, an electrode in contact with the subject, and an opposite surface of the sticking surface of the pressure-sensitive adhesive layer. A base material layer provided on top of the base material layer, an electronic device provided on the base material layer, having an integrated circuit and an information processing device, and processing analog data acquired via the electrodes, and the base material layer. The integrated circuit includes a first input terminal connected to the electrode and analog data input via the first input terminal, including a circuit unit for connecting the electrode and the electronic device. The information processing apparatus has a second input terminal connected to the output terminal, and has an A / D converter for converting digital data and an output terminal, and a control unit of the integrated circuit has the digital. Data is output from the output terminal to the information processing apparatus.

It is possible to provide a stick-on biosensor suitable for a disposable type.

It is an exploded view which shows the sticking type biological sensor 100 of embodiment. It is a figure which shows the cross section of the completed state corresponding to the cross section of AA of FIG. It is a figure which shows the circuit structure of the sticking type biosensor 100. FIG. 4 is a diagram showing an electronic device 150. It is a figure which shows the structure of ASIC150A. It is a timing chart which shows the processing of MPU150B. It is a flowchart which shows the process of MPU150B.

Hereinafter, embodiments to which the stick-on biosensor of the present invention is applied will be described.

<Embodiment>
FIG. 1 is an exploded view showing the stick-on biosensor 100 of the embodiment. FIG. 2 is a diagram showing a cross section in a completed state corresponding to the cross section taken along the line AA of FIG. The stick-on biosensor 100 includes a pressure-sensitive adhesive layer 110, a base material layer 120, a circuit unit 130, a substrate 135, a probe 140, a fixing tape 145, an electronic device 150, a battery 160, and a cover 170 as main components. ..

In the following, the XYZ coordinate system will be defined and described. In the following, for convenience of explanation, the negative side of the Z axis is referred to as the lower side or the lower side, and the positive side of the Z axis is referred to as the upper side or the upper side, but does not represent a universal hierarchical relationship.

In the present embodiment, as an example, a stick-on biosensor 100 that is brought into contact with a living body as a subject to measure biological information will be described. The living body means a human body and an organism other than the human body, and is attached to the skin, scalp, forehead, or the like. As an example, the stick-on biosensor 100 passes data representing the waveform of the biological signal acquired by the user of the stick-on biosensor 100 to a medical institution, acquires the diagnosis result of the doctor's diagnosis, and uses the acquired diagnosis result. It is provided to the user by the vendor who provides it to the user. The stick-on biosensor 100 is a disposable type. The disposable type means that it is used only once and is not reused or regenerated (reused by replacing a part of the configuration with a new one). Hereinafter, each member constituting the stick-on biosensor 100 will be described.

In the following, an electrode that comes into contact with a living body as a subject will be referred to as a probe 140, and a fixing tape 145 will be used as an example of a joint portion. A pair of electrodes as the probe 140 is provided in order to measure biological information in a single channel. Single channel means to acquire one biometric information from a pair of (two) electrodes.

The stick-on biosensor 100 is a sheet-like member having a substantially elliptical shape in a plan view. In the stick-on type biosensor 100, the upper surface side opposite to the lower surface (the surface on the −Z direction side) to be attached to the skin 10 of the living body is covered with the cover 170. The lower surface of the stick-on biosensor 100 is a stick-on surface.

The circuit unit 130 and the substrate 135 are mounted on the upper surface of the substrate layer 120. Further, the probe 140 is provided so as to be embedded in the pressure-sensitive adhesive layer 110 so as to be exposed from the lower surface 112 of the pressure-sensitive adhesive layer 110. The lower surface 112 is a sticking surface of the sticking type biosensor 100.

The pressure-sensitive adhesive layer 110 is a flat-plate adhesive layer. The pressure-sensitive adhesive layer 110 has a longitudinal direction in the X-axis direction and a lateral direction in the Y-axis direction. The pressure-sensitive adhesive layer 110 is supported by the base material layer 120, and is attached to the lower surface 121 of the base material layer 120 on the −Z direction side.

As shown in FIG. 2, the pressure-sensitive adhesive layer 110 has an upper surface 111 and a lower surface 112. The upper surface 111 and the lower surface 112 are flat surfaces. The pressure-sensitive adhesive layer 110 is a layer in which the stick-on biosensor 100 comes into contact with the living body. Since the lower surface 112 has pressure-sensitive adhesiveness, it can be attached to the skin 10 of a living body. The lower surface 112 is the lower surface of the stickable biological sensor 100, and can be attached to the surface of the living body such as the skin 10.

Further, the pressure-sensitive adhesive layer 110 has a through hole 113. The through hole 113 has the same size and position as the through hole 123 of the base material layer 120 in a plan view, and communicates with the through hole 123.

The material of the pressure-sensitive adhesive layer 110 is not particularly limited as long as it has pressure-sensitive adhesiveness, and examples thereof include materials having biocompatibility. Examples of the material of the pressure-sensitive adhesive layer 110 include an acrylic pressure-sensitive adhesive and a silicone-based pressure-sensitive adhesive. Acrylic pressure-sensitive adhesives are preferable.

The acrylic pressure-sensitive adhesive contains an acrylic polymer as a main component.

Acrylic polymer is a pressure sensitive adhesive component. The acrylic polymer contains a (meth) acrylic acid ester such as isononyl acrylate and methoxyethyl acrylate as a main component, and a monomer component copolymerizing with a (meth) acrylic acid ester such as acrylic acid as an optional component. A polymer obtained by polymerizing the above can be used. The content of the main component in the monomer component is 70% by mass to 99% by mass, and the content of the optional component in the monomer component is 1% by mass to 30% by mass. As the acrylic polymer, for example, the (meth) acrylic acid ester-based polymer described in JP-A-2003-342541 can be used.

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

The carboxylic acid ester contained in the acrylic pressure-sensitive adhesive is a pressure-sensitive adhesive force adjusting agent that reduces the pressure-sensitive adhesive force of the acrylic polymer and adjusts the pressure-sensitive adhesive force of the pressure-sensitive adhesive layer 110. The carboxylic acid ester is a carboxylic acid ester compatible with an acrylic polymer.

Specifically, the carboxylic acid ester is, for example, the trifatty acid glyceryl.

The content ratio of the carboxylic acid ester is preferably 30 parts by mass to 100 parts by mass, and more preferably 50 parts by mass to 70 parts by mass or less with respect to 100 parts by mass of the acrylic polymer.

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

The content of the cross-linking agent is preferably, for example, 0.001 part by mass to 10 parts by mass, and more preferably 0.01 part by mass to 1 part by mass with respect to 100 parts by mass of the acrylic polymer.

The pressure-sensitive adhesive layer 110 preferably has excellent biocompatibility. For example, when the pressure-sensitive adhesive layer 110 is subjected to a keratin peeling test, the keratin peeling area ratio is preferably 0% to 50%, more preferably 1% to 15%. When the keratin exfoliation area ratio is in the range of 0% to 50%, the load on the skin 10 (see FIG. 2) can be suppressed even if the pressure-sensitive adhesive layer 110 is attached to the skin 10 (see FIG. 2). The keratin exfoliation test is measured by the method described in JP-A-2004-83425.

The moisture permeability of the pressure-sensitive adhesive layer 110 is preferably 300 (g / m ² / day) or more, more preferably 600 (g / m ² / day) or more, and 1000 (g / m ² / day) or more. Day) or more is more preferable. If the moisture permeability of the pressure-sensitive adhesive layer 110 is 300 (g / m ² / day) or more, even if the pressure-sensitive adhesive layer 110 is attached to the skin 10 of a living body (see FIG. 2), the skin 10 (FIG. 2). The load of (see) can be suppressed.

The pressure-sensitive adhesive layer 110 satisfies at least one of the requirements that the keratin peeling area ratio in the keratin peeling test is 50% or less and the moisture permeability is 300 (g / m ² / day) or more. The pressure-sensitive adhesive layer 110 is biocompatible. It is more preferable that the material of the pressure-sensitive adhesive layer 110 satisfies both of the above requirements. As a result, the pressure-sensitive adhesive layer 110 is more stable and has high biocompatibility.

The thickness between the upper surface 111 and the lower surface 112 of the pressure-sensitive adhesive layer 110 is preferably 10 μm to 300 μm. When the thickness of the pressure-sensitive adhesive layer 110 is 10 μm to 300 μm, the stick-on biosensor 100 can be made thinner, and in particular, the area other than the electronic device 150 and the battery 160 in the stick-on biosensor 100 can be made thinner.

The base material layer 120 is a support layer that supports the pressure-sensitive adhesive layer 110, and the pressure-sensitive adhesive layer 110 is adhered to the lower surface 121 of the base material layer 120. The circuit unit 130 and the substrate 135 are arranged on the upper surface side of the base material layer 120.

The base material layer 120 is a flat plate-shaped (sheet-shaped) member made of an insulator. The shape of the base material layer 120 in a plan view is the same as the shape of the pressure-sensitive adhesive layer 110 in a plan view, and they are aligned and overlapped in a plan view.

The base material layer 120 has a lower surface 121 and an upper surface 122. The lower surface 121 and the upper surface 122 are flat surfaces. The lower surface 121 is in contact with the upper surface 111 of the pressure-sensitive adhesive layer 110 (pressure-sensitive adhesion). The base material layer 120 may be made of a flexible resin having appropriate elasticity, flexibility and toughness. For example, a polyurethane resin, a silicone resin, an acrylic resin, a polystyrene resin, or a vinyl chloride resin. , And a thermoplastic resin such as a polyester resin. The thickness of the base material layer 120 is preferably 1 μm to 300 μm, more preferably 5 μm to 100 μm, and even more preferably 10 μm to 50 μm.

The circuit unit 130 has a wiring 131, a frame 132, and a substrate 133. More specifically, the circuit unit 130 is connected to the electrode via the frame 132, and is connected to the electronic device 160 via the wiring 131. The stick-on biosensor 100 includes two such circuit units 130. The wiring 131 and the frame 132 are provided on the upper surface of the substrate 133 and are integrally formed. The wiring 131 connects the frame 132 with the electronic device 150 and the battery 160.

The wiring 131 and the frame 132 can be made of copper, nickel, gold, an alloy thereof, or the like. The thickness of the wiring 131 and the frame 132 is preferably 0.1 μm to 100 μm, more preferably 1 μm to 50 μm, and even more preferably 5 μm to 30 μm.

The two circuit units 130 are provided corresponding to the two through holes 113 and 123 of the pressure-sensitive adhesive layer 110 and the base material layer 120, respectively. The wiring 131 is connected to the electronic device 150 and the terminal 135A for the battery 160 via the wiring of the substrate 135. The frame 132 is a rectangular annular conductive member larger than the opening of the through hole 123 of the base material layer 120.

The substrate 133 has the same shape as the wiring 131 and the frame 132 in a plan view. The portion of the substrate 133 where the frame 132 is provided has a rectangular annular shape larger than the opening of the through hole 123 of the substrate layer 120. The frame 132 and the rectangular annular portion of the substrate 133 on which the frame 132 is provided are provided so as to surround the through hole 123 on the upper surface of the base material layer 120. The substrate 133 may be made of an insulator, and for example, a polyimide substrate or a film can be used. Since the base material layer 120 has adhesiveness (tackiness), the substrate 133 is fixed to the upper surface of the base material layer 120.

The substrate 135 is an insulator-made substrate on which the electronic device 150 and the battery 160 are mounted, and is provided on the upper surface 122 of the base material layer 120. The substrate 135 is fixed by the tackiness (adhesiveness) of the base material layer. As the substrate 135, a polyimide substrate or a film can be used as an example. Wiring and terminals 135A for the battery 160 are provided on the upper surface of the substrate 135. The wiring of the board 135 is connected to the electronic device 150 and the terminal 135A, and is also connected to the wiring 131 of the circuit unit 130.

The probe 140 is an electrode that comes into contact with the subject. Specifically, the probe 140 is an electrode that comes into contact with the skin 10 and detects a biological signal when the pressure-sensitive adhesive layer 110 is attached to the skin 10. The biological signal is, for example, an electric signal representing an electrocardiographic waveform, an electroencephalogram, a pulse, or the like, and more specifically, a signal representing analog electrocardiographic data. The biological signal represents the potential difference detected by the two probes 140.

The electrode used as the probe 140 is manufactured by using a conductive composition containing at least a conductive polymer and a binder resin as described later. Further, the electrode is manufactured by punching a sheet-shaped member obtained by using the conductive composition with a mold or the like, and is used as a probe.

The probe 140 has a rectangular shape in a plan view, is larger than the through holes 113 and 123 of the pressure-sensitive adhesive layer 110 and the base material layer 120, and has holes 140A arranged in a matrix. At the ends (parts of the four ends) of the probe 140 in the X and Y directions, the ladder-shaped sides of the probe 140 may protrude. The electrode used as the probe 140 may have a predetermined pattern shape. Examples of the predetermined electrode pattern shape include a mesh shape, a stripe shape, and a shape in which a plurality of electrodes are exposed from the sticking surface.

The fixing tape 145 is an example of the joint portion of the present embodiment. The fixing tape 145 is, for example, a rectangular annular copper tape. An adhesive is applied to the lower surface of the fixing tape 145. The fixing tape 145 is provided on the frame 132 so as to surround the four sides of the probe 140 outside the openings of the through holes 113 and 123 in a plan view, and fixes the probe 140 to the frame 132. The fixing tape 145 may be a metal tape other than copper.

The fixing tape 145 may be a non-conductive tape such as a resin tape composed of a non-conductive resin base material and an adhesive, in addition to a tape having a metal layer such as a copper tape. A conductive tape such as a metal tape is preferable because the probe 140 can be bonded (fixed) to the frame 132 of the circuit unit 130 and electrically connected.

The probe 140 is fixed to the frame 132 by a rectangular annular fixing tape 145 that covers the four end portions, with the four end portions arranged on the frame 132. The fixing tape 145 is adhered to the frame 132 through a gap such as a hole 140A of the probe 140.

With the four ends of the probe 140 fixed to the frame 132 with the fixing tape 145 in this way, the pressure-sensitive adhesive layer 110A and the base material layer 120A are laminated on the fixing tape 145 and the probe 140 to form a pressure-sensitive adhesive layer. When the 110A and the base material layer 120A are pressed downward, the probe 140 is pushed along the inner walls of the through holes 113 and 123, and the pressure-sensitive adhesive layer 110A is pushed into the hole 140A of the probe 140.

The probe 140 is pushed down to a position where the central portion is substantially flush with the lower surface 112 of the pressure-sensitive adhesive layer 110 while the four end portions are fixed to the frame 132 by the fixing tape 145. Therefore, when the probe 140 is applied to the skin 10 of a living body (see FIG. 2), the pressure-sensitive adhesive layer 110A is adhered to the skin 10 and the probe 140 can be brought into close contact with the skin 10.

The thickness of the probe 140 is preferably thinner than the thickness of the pressure-sensitive adhesive layer 110. The thickness of the probe 140 is preferably 0.1 μm to 100 μm, more preferably 1 μm to 50 μm.

Further, the peripheral portion (rectangular annular portion) surrounding the central portion in the plan view of the pressure-sensitive adhesive layer 110A is located on the fixing tape 145. In FIG. 2, the upper surface of the pressure-sensitive adhesive layer 110A is substantially flat, but the central portion may be recessed below the peripheral portion. The base material layer 120A is superposed on a substantially flat upper surface of the pressure sensitive adhesive layer 110A.

Such the pressure-sensitive adhesive layer 110A and the base material layer 120A may be made of the same material as the pressure-sensitive adhesive layer 110 and the base material layer 120, respectively. Further, the pressure-sensitive adhesive layer 110A may be made of a material different from that of the pressure-sensitive adhesive layer 110. Further, the base material layer 120A may be made of a material different from that of the base material layer 120.

Although the thickness of each part is exaggerated in FIG. 2, in reality, the thickness of the pressure-sensitive adhesive layers 110 and 110A is 10 μm to 300 μm, and the thickness of the base material layers 120 and 120A is 1 μm to 300 μm. Is. The thickness of the wiring 131 is 0.1 μm to 100 μm, the thickness of the substrate 133 is about several hundred μm, and the thickness of the fixing tape 145 is 10 μm to 300 μm.

Further, as shown in FIG. 2, when the probe 140 and the frame 132 are in direct contact with each other to ensure an electrical connection, the fixing tape 145 may be a non-conductive resin tape or the like. Good.

Further, in FIG. 2, the fixing tape 145 covers the side surfaces of the frame 132 and the substrate 133 in addition to the probe 140, and reaches the upper surface of the base material layer 120. However, since the fixing tape 145 only needs to be able to bond the probe 140 and the frame 132, the fixing tape 145 does not have to reach the upper surface of the base material layer 120, does not have to cover the side surface of the substrate 133, and covers the side surface of the frame 132. It does not have to be covered.

Further, the substrate 133 and the two substrates 135 may be one integrated substrate. In this case, wiring 131, two frames 132, and terminal 135A are provided on the surface of one substrate, and the electronic device 150 and the battery 160 are mounted.

The electrode used as the probe 140 is preferably manufactured by thermosetting the following conductive composition and molding it. The conductive composition contains a conductive polymer, a binder resin, and at least one of a cross-linking agent and a plasticizer.

As the conductive polymer, for example, polythiophene, polyacetylene, polypyrrole, polyaniline, polyphenylene vinylene and the like can be used. These may be used alone or in combination of two or more. Among these, it is preferable to use a polythiophene compound. PEDOT / PSS doped with polystyrene sulfonic acid (poly4-styrene sulfonate; PSS) to poly 3,4-ethylenedioxythiophene (PEDOT) because it has lower contact impedance with the living body and has high conductivity. Is more preferable to use.

The content of the conductive polymer is preferably 0.20 parts by mass to 20 parts by mass with respect to 100 parts by mass of the conductive composition. When the content is within the above range, excellent conductivity, toughness and flexibility can be imparted to the conductive composition. The content of the conductive polymer is more preferably 2.5 parts by mass to 15 parts by mass, and further preferably 3.0 parts by mass to 12 parts by mass with respect to the conductive composition.

As the binder resin, a water-soluble polymer, a water-insoluble polymer, or the like can be used. As the binder resin, it is preferable to use a water-soluble polymer from the viewpoint of compatibility with other components contained in the conductive composition. The water-soluble polymer contains a polymer (hydrophilic polymer) that is completely insoluble in water and has hydrophilicity.

As the water-soluble polymer, a hydroxyl group-containing polymer or the like can be used. As the hydroxyl group-containing polymer, saccharides such as agarose, polyvinyl alcohol (PVA), modified polyvinyl alcohol, or a copolymer of acrylate and sodium acrylate can be used. These may be used alone or in combination of two or more. Among these, polyvinyl alcohol or modified polyvinyl alcohol is preferable, and modified polyvinyl alcohol is more preferable.

Examples of the modified polyvinyl alcohol include acetacetyl group-containing polyvinyl alcohol and diacetone acrylamide modified polyvinyl alcohol. As the diacetone acrylamide-modified polyvinyl alcohol, for example, a diacetone acrylamide-modified polyvinyl alcohol-based resin (DA-modified PVA-based resin) described in JP-A-2016-166436 can be used.

The content of the binder resin is preferably 5 parts by mass to 140 parts by mass with respect to 100 parts by mass of the conductive composition. When the content is within the above range, excellent conductivity, toughness and flexibility can be imparted to the conductive composition. The content of the binder resin is more preferably 10 parts by mass to 100 parts by mass, and further preferably 20 parts by mass to 70 parts by mass with respect to the conductive composition.

The cross-linking agent and the plasticizer have a function of imparting toughness and flexibility to the conductive composition. By imparting flexibility to the molded product of the conductive composition, an electrode having elasticity was obtained. As a result, the probe 140 having elasticity can be produced.

The toughness is a property that achieves both excellent strength and elongation. The toughness does not include the property that one of the strength and the elongation is remarkably excellent, but the other is remarkably low, and includes the property of having an excellent balance of both strength and elongation.

Flexibility is a property that can suppress the occurrence of damage such as breakage in the bent portion after bending the molded body (electrode sheet) of the conductive composition.

The cross-linking agent cross-links the binder resin. By including the cross-linking agent in the binder resin, the toughness of the conductive composition can be improved. The cross-linking agent preferably has reactivity with a hydroxyl group. If the cross-linking agent has reactivity with a hydroxyl group, the cross-linking agent can react with the hydroxyl group of the hydroxyl group-containing polymer when the binder resin is a hydroxyl group-containing polymer.

Examples of the cross-linking agent include zirconium compounds such as zirconium salts; titanium compounds such as titanium salts; borides such as boric acid; isocyanate compounds such as blocked isocyanate; aldehyde compounds such as dialdehyde such as glyoxal; alkoxyl group-containing compounds and methylol groups. Examples include contained compounds. These may be used alone or in combination of two or more. Of these, a zirconium compound, an isocyanate compound, or an aldehyde compound is preferable from the viewpoint of reactivity and safety.

The content of the cross-linking agent is preferably 0.2 parts by mass to 80 parts by mass with respect to 100 parts by mass of the conductive composition. When the content is within the above range, excellent toughness and flexibility can be imparted to the conductive composition. The content of the cross-linking agent is more preferably 1 part by mass to 40 parts by mass, and more preferably 3.0 parts by mass to 20 parts by mass.

The plasticizer improves the tensile elongation and flexibility of the conductive composition. Examples of the plasticizer include glycerin, ethylene glycol, propylene glycol, sorbitol, and polyol compounds such as N-methylpyrrolidone (NMP), dimethylformamide (DMF), NN'-dimethylacetamide (DMAc), and dimethyl sulfoxide. Examples thereof include aprotic compounds such as (DMSO). These may be used alone or in combination of two or more. Among these, glycerin is preferable from the viewpoint of compatibility with other components.

The content of the plasticizer is preferably 0.2 parts by mass to 150 parts by mass with respect to 100 parts by mass of the conductive composition. When the content is within the above range, excellent toughness and flexibility can be imparted to the conductive composition. The content of the plasticizer is more preferably 1.0 part by mass to 90 parts by mass, and further preferably 10 parts by mass to 70 parts by mass with respect to 100 parts by mass of the conductive polymer.

At least one of the cross-linking agent and the plasticizer may be contained in the conductive composition. By including at least one of the cross-linking agent and the plasticizer in the conductive composition, the molded product of the conductive composition can improve toughness and flexibility.

When the conductive composition contains a cross-linking agent but no plasticizer, the molded product of the conductive composition can further improve toughness, that is, both tensile strength and tensile elongation, and is flexible. It is possible to improve the sex.

When the conductive composition contains a plasticizer but does not contain a cross-linking agent, the tensile elongation of the molded product of the conductive composition can be improved, so that the molded product of the conductive composition is tough as a whole. Can be improved. In addition, the flexibility of the molded product of the conductive composition can be improved.

It is preferable that both the cross-linking agent and the plasticizer are contained in the conductive composition. By including both the cross-linking agent and the plasticizer in the conductive composition, the molded product of the conductive composition is imparted with even better toughness.

In addition to the above components, the conductive composition may contain a surfactant, a softener, a stabilizer, a leveling agent, an antioxidant, an antioxidant, a leavening agent, a thickener, a colorant, or, if necessary. Various known additives such as a filler can be appropriately contained in an arbitrary ratio. Examples of the surfactant include silicone-based surfactants.

The conductive composition is prepared by mixing the above-mentioned components in the above-mentioned ratios.

The conductive composition can appropriately contain a solvent in an arbitrary ratio, if necessary. As a result, an aqueous solution of the conductive composition (an aqueous solution of the conductive composition) is prepared.

As the solvent, an organic solvent or an aqueous solvent can be used. Examples of the organic solvent include ketones such as acetone and methyl ethyl ketone (MEK); esters such as ethyl acetate; ethers such as propylene glycol monomethyl ether; and amides such as N, N-dimethylformamide. Examples of the aqueous solvent include water; methanol, ethanol, propanol, alcohol for isopropanol, and the like. Among these, it is preferable to use an aqueous solvent.

Any one or more of the conductive polymer, the binder resin, and the cross-linking agent may be used as an aqueous solution dissolved in a solvent. In this case, the above-mentioned aqueous solvent is preferable as the solvent.

The electronic device 150 is installed on the upper surface 122 of the base material layer 120 and is electrically connected to the wiring 131. The electronic device 150 processes a biological signal acquired via an electrode used as a probe 140. The electronic device 150 has a rectangular shape in a cross-sectional view. Terminals are provided on the lower surface (-Z direction) of the electronic device 150. Examples of the material for the terminals of the electronic device 150 include solder, conductive paste, and the like.

As shown in FIG. 1, the electronic device 150 includes an ASIC (application specific integrated circuit) 150A, an MPU (Micro Processing Unit) 150B, a memory 150C, and a wireless communication unit 150TR as an example, and includes a circuit unit. It is connected to the probe 140 and the battery 160 via 130.

The ASIC 150A includes an A / D (Analog to digital) converter. The electronic device 150 is driven by the power supplied by the battery 160 and acquires an analog biological signal measured by the probe 140. Hereinafter, electrocardiographic data will be taken up and described as an example of biological signals. The electronic device 150 performs processing such as filtering and digital conversion on the analog biological signal, and the MPU 150B obtains the summed average value of the digital biological signal obtained by digitally converting the analog biological signal acquired a plurality of times and stores it in the memory 150C. .. As an example, the electronic device 150 can continuously acquire an analog biological signal for 24 hours or more. Since the electronic device 150 may measure a biological signal (for example, analog electrocardiographic data) for a long period of time, it is devised to reduce power consumption. Further, the manufacturing cost of the electronic device 150 is reduced by adopting a configuration in which the ASIC 150A performs digital conversion processing of an analog biological signal, which contributes to the realization of a disposable stickable biological sensor 100.

The wireless communication unit 150TR is a transceiver used when the test device of the evaluation test reads out the digital biological signal stored in the memory 150C in the evaluation test by wireless communication, and communicates at 2.4 GHz as an example. The evaluation test is, for example, a JIS 60601-2-47 standard test. The evaluation test is a test for confirming the operation performed after the completion of the biological sensor that detects a biological signal as a medical device. The evaluation test requires that the attenuation rate of the biological signal extracted from the biological sensor is less than 5% with respect to the biological signal input to the biological sensor. This evaluation test is performed on all finished products.

In addition, the start command of the evaluation test, the start command of the 24H measurement, etc. can be sent to the wireless communication unit through, for example, a smartphone on which a dedicated application program of the stickable biosensor 100 is installed or a function on a web browser of a PC (Personal Computer). It is input to MPU150B via 150TR.

Although the form in which the electronic device 150 includes the wireless communication unit 150TR will be described here, instead of the wireless communication unit 150TR, a connector for connecting the cable of the test device may be included, and the biological signal may be read out via the connector. ..

As shown in FIG. 2, the battery 160 is provided on the upper surface 122 of the base material layer 120. As the battery 160, a lead storage battery, a lithium ion secondary battery, or the like can be used. The battery 160 may be a button battery type. The battery 160 is an example of a battery. The battery 160 has terminals (not shown) provided on its lower surface. The terminals of the battery 160 are connected to the probe 140 and the electronic device 150 via the circuit unit 130. The capacity of the battery 160 is set so that, for example, the electronic device 150 can measure a biological signal (for example, analog electrocardiographic data) for 24 hours or more.

The cover 170 covers the base material layer 120, the circuit unit 130, the substrate 135, the probe 140, the fixing tape 145, the electronic device 150, and the battery 160. The cover 170 has a base 170A and a protrusion 170B protruding from the center of the base 170A in the + Z direction. The base portion 170A is a portion located around the cover 170 in a plan view, and is a portion lower than the protruding portion 170B. A recess 170C is provided on the lower side of the protrusion 170B. In the cover 170, the lower surface of the base 170A is adhered to the upper surface 122 of the base material layer 120. The substrate 135, the electronic device 150, and the battery 160 are housed in the recess 170C. The cover 170 is adhered to the upper surface 122 of the base material layer 120 with the electronic device 150, the battery 160, and the like housed in the recess 170C.

The cover 170 not only serves as a cover for protecting the circuit unit 130, the electronic device 150, and the battery 160 on the base material layer 120, but also provides internal components from the impact applied to the stickable biosensor 100 from the upper surface side. It has a role as a protective shock absorbing layer. As the cover 170, for example, silicone rubber, soft resin, urethane or the like can be used.

FIG. 3 is a diagram showing a circuit configuration of the stick-on biosensor 100. Each probe 140 is connected to the electronic device 150 and the battery 160 via the wiring 131 and the wiring 135B of the substrate 135. The two probes 140 are connected in parallel to the electronic device 150 and the battery 160.

Next, the details of the electronic device 150 will be described with reference to FIG. FIG. 4 is a diagram showing an electronic device 150.

The electronic device 150 includes an ASIC (application specific integrated circuit) 150A, an MPU (Micro Processing Unit) 150B, a memory 150C, a bus 150D, 150E, a crystal oscillator 60, 70, an RC oscillator 80, and a switch 90. Have. The buses 150D and 150E are, for example, SPI (Serial Peripheral Interface) buses.

The ASIC 150A is connected to the probe 140 via the wiring 131 outside the electronic device 150, and is connected to the MPU 150B via the bus 150D inside the electronic device 150. Further, a crystal oscillator 60 is connected to the ASIC 150A.

The ASIC 150A has an ADC (Analog to Digital Converter, AD converter) 151A, terminals 152A, and a pair of terminals 153A. Components other than the ADC 151A, terminals 152A, and pair of terminals 153A of the ASIC 150A will be described later with reference to FIG.

The ASIC 150A has a terminal corresponding to the SPI interface. The ASIC 150A is a slave device, operates in response to a command from the master device MPU 150B, and transmits a signal indicating the operation result to the MPU 150B. The ASIC 150A operates in response to a command received from the MPU 150B. Here, the master device is a device that controls the control of a plurality of devices when the plurality of devices perform a cooperative operation. A slave device is a device that operates according to a command or control from a master device when a plurality of devices perform cooperative operations.

As an example, the ADC 151A is a SAR (Successive Approximation Register) / SF (Stochastic Flash) type AD converter, and for example, the A / D converter described in JP-A-2016-092648 is used. Can be done.

The ADC 151A converts an analog biological signal (for example, electrocardiographic data) acquired by the probe 140 into a digital biological signal and outputs it to the MPU 150B.

The terminal 152A is connected to the MPU 150B via the bus 150D. There are actually a plurality of terminals 152A, including a terminal for outputting a digital biological signal or the like to the MPU 150B, a terminal for inputting a command from the MPU 150B, a terminal for transmitting the operation result of the ASIC 150A to the MPU 150B, and a clock terminal or the like. .. Of the plurality of terminals 152A, the terminal that outputs a digital biological signal to the MPU 150B is an example of an output terminal.

The pair of terminals 153A is an example of a pair of first input terminals, to which a pair of probes 140 are connected and an analog biological signal is input.

Further, the ASIC 150A divides the 32 MHz clock oscillated by the crystal oscillator 60 to generate a 4 MHz system clock used internally. This configuration will be described later with reference to FIG.

The MPU 150B is an example of an information processing device, and is connected to the ASIC 150A via the bus 150D and connected to the memory 150C via the bus 150E. Further, the RC oscillator 80 and the crystal oscillator 70 are connected to the MPU 150B via a switch 90. The switch 90 is a switch that selectively connects either one of the crystal oscillator 70 and the RC oscillator 80 to the MPU 150B, and the switch 90 is switched by the MPU 150B.

The RC oscillator 80 outputs a clock having a frequency lower than that of the clock output by the crystal oscillator 70. The RC oscillator 80 has a lower clock frequency and lower accuracy than the crystal oscillator 70, but consumes less power than the crystal oscillator 70.

The crystal oscillator 70 and the RC oscillator 80 are switched on / off by the MPU 150B. When the crystal oscillator 70 is on, the RC oscillator 80 is turned off, and when the RC oscillator 80 is on, the crystal oscillator 70 is turned off.

The MPU 150B has a main control unit 151B, a calculation unit 153B, a memory 154B, and terminals 155B and 156B. The main control unit 151B and the arithmetic unit 153B represent the functions realized by the computer that realizes the MPU 150B, and the memory 154B functionally represents the memory of the computer that realizes the MPU 150B.

The main control unit 151B is a processing unit that controls the processing of the MPU 150B, and executes processing other than the processing executed by the calculation unit 153B.

The calculation unit 153B executes a process of calculating the added value of the digital biological signal input from the ASIC 150A and a process of calculating the average value of the added values. Here, as an example, the calculation unit 153B performs an addition process every time a digital biological signal is acquired from the ASIC 150A, and calculates an average value every time an additional value of eight digital biological signals is obtained. When the calculation unit 153B calculates the average value, it stores it in the memory 150C.

The memory 154B stores programs and data necessary for the main control unit 151B and the arithmetic unit 153B of the MPU 150B to execute processing. Further, the memory 154B holds the added value obtained by the addition process of the calculation unit 153B.

There are actually a plurality of terminals 155B, including a terminal for inputting a digital biological signal from the ASIC 150A, a terminal for outputting a command to the ASIC 150A, a terminal for receiving a signal indicating an operation result of the ASIC 150A, and a clock terminal. Of the plurality of terminals 155B, the terminal to which the digital biological signal is input from the ASIC 150A is an example of the second input terminal.

The terminal 156B is an output terminal that is connected to the PC 50 via a cable 51 and outputs a digital biological signal to the memory 150C.

Further, the MPU 150B generates a system clock to be used internally based on the clock oscillated by the crystal oscillator 70 or the RC oscillator 80. More specifically, the main control unit 151B performs a process of oscillating the crystal oscillator 70. The main control unit 151B and the crystal oscillator 70 construct a crystal oscillator.

The main control unit 151B sets the system clock frequency high (32 MHz as an example) in order to set the operating frequency high until the MPU 150B transmits a command to start the biological signal acquisition process to the ASIC 150A. Is executing the biosignal acquisition process, the system clock frequency is set low (4 MHz as an example) in order to lower the operating frequency. The biological signal acquisition process is a process in which the ASIC 150A acquires an analog biological signal and digitally converts it into a digital biological signal.

At this time, the main control unit 151B switches the crystal oscillator 70 and the RC oscillator 80 on / off. The frequency of the clock output by the crystal oscillator 70 is 32 MHz as an example, and the frequency of the clock output by the RC oscillator 80 is 16 MHz as an example. The main control unit 151B generates the system clock of the MPU 150B from the clock output from either the crystal oscillator 70 or the RC oscillator 80 by switching the switch 90.

The main control unit 151B uses the 32 MHz clock output by the crystal oscillator 70 as it is as the system clock until the MPU 150B transmits a command to start the biological signal acquisition process to the ASIC 150A. Further, when the MPU 150B transmits a command to start the acquisition process of the biological signal to the ASIC 150A, the main control unit 151B divides the 32 MHz clock output by the crystal oscillator 70 separately from the 32 MHz system clock. Generates a 4 MHz clock. The MPU 150B outputs a 4 MHz clock to the ASIC 150A when the ASIC 150A performs a biological signal acquisition process. The 4 MHz clock is output to the ASIC 150A from the CLK terminal of the terminals 155B.

The main control unit 151B divides the clock of the RC oscillator 80 to generate a system clock of 4 MHz, and corrects the timing of the system clock by using the CS (Chip Select) signal input from the ASIC 150A as a trigger. In this way, the main control unit 151B synchronizes the 4 MHz system clock obtained by dividing the clock of the RC oscillator 80 with the CS signal. The 4 MHz clock is output to the ASIC 150A from the CLK terminal of the terminals 155B.

The MPU 150B generates a 4 MHz system clock based on the clock of the RC oscillator 80 because the power consumption of the MPU 150B is reduced by lowering the frequency of the system clock when the ASIC 150A is performing the biological signal acquisition process. Because. The crystal oscillator 70 is used before the MPU 150B sends a command to start the biological signal acquisition process to the ASIC 150A and after sending a command to end the biological signal acquisition process, and the MPU 150B uses the ASIC 150A to acquire the biological signal. It is not used during processing.

The memory 150C is connected to the MPU 150B via the bus 150E. The memory 150C is, for example, a NAND flash memory. As an example, the stick-on biosensor 100 is stuck on the chest of a living body for about 24 hours, acquires an analog biological signal (for example, analog electrocardiographic data), and converts it into a digital biological signal (for example, digital electrocardiographic data). After performing the addition averaging process, the data is stored in the memory 150C. Therefore, the memory 150C has a capacity capable of storing biological signals (for example, electrocardiographic data) for 24 hours.

The memory 150C has terminals 151C. A cable 51 connected to the PC 50 can be connected to the terminal 151C. The biological signal stored in the memory 150C can be transferred to the PC 50 via the cable 51.

FIG. 5 is a diagram showing the configuration of the ASIC 150A. The ASIC150A includes an input terminal (VINP) 201, an input terminal (VINN) 202, a CLK terminal 203, a terminal 152A, an LNA (Low Noise Amplifier) 210, a BUF (Buffer, a buffer) 220, an LPF (Low Pass Filter) 230, an ADC 151A, It includes a bias circuit 240, a clock generator 250, an oscillator 260, a control unit 270, and a level shifter 280.

In addition to these, the ASIC150A includes a VREG terminal, a VCOM terminal, a VMID terminal, a VCS terminal, a TAB terminal (GND potential), a GND terminal, a VDD terminal (1.2), a VDDLV terminal (1.5V to 2.5V), and the like. including.

The input terminals 201 and 202 are connected to the probe 140 via the wiring 131. A + (positive) signal is input to the input terminal 201, and a − (negative) signal is input to the input terminal 201.

The CLK terminal 203 is connected to a crystal oscillator 60 provided outside the ASIC 150A.

The terminal 152A is connected to the MPU 150B as described with reference to FIG.

The LNA 210 is connected between the input terminals 201 and 202 and the BUF 220, and amplifies and outputs an analog biological signal input from the input terminals 201 and 202.

The BUF 220 is connected between the LNA 210 and the ADC 151A, and shapes the waveform of the analog biological signal amplified by the LNA 210 and outputs it to the LPF 230.

The LPF 230 is connected between the BUF 220 and the ADC 151A, and passes only a predetermined band component on the low frequency side of the analog biological signal input from the BUF 220 in order to remove noise.

The ADC 151A operates based on the clock signal input from the clock generator 250, converts the analog biological signal input from the LPF 230 into a digital biological signal, and outputs the analog biological signal to the control unit 270. The clock signal input from the clock generator 250 is a clock signal that determines the sampling period of the ADC 151A, and is 4 MHz as an example. The frequency of the clock signal input from the clock generator 250 is set lower than the system clock (32 MHz as an example) used inside the MPU 150B when the MPU 150B transmits a command to the ASIC 150A.

The bias circuit 240 is a circuit that converts the power supply voltage (1.2V) input to the VCS terminal into the voltage required by the ADC 151A (0.5V and 0.25V as an example) and outputs the voltage. The bias circuit 240 is, for example, a voltage divider circuit.

The clock generator 250 includes a PLL (Phase Locked Loop) and a frequency divider, and generates a clock having a predetermined frequency (4 MHz as an example) from the clocks input from the crystal oscillator 60 and the oscillator 260 to generate the ADC 151A and the control unit. Output to 270 etc. The clock generator 250 divides the 32 MHz clock output from the crystal oscillator 60 to generate a 4 MHz system clock internally used by the ASIC 150A. The clock generator 250 outputs the divided 4 MHz system clock to the ADC 151A, the control unit 270, and the like.

The oscillator 260 is an IC (Integrated Circuit) that oscillates the crystal oscillator 60. The oscillator 260 and the crystal oscillator 60 construct a crystal oscillator. The oscillator 260 and the crystal oscillator 60 oscillate a clock of 32 MHz as an example.

The control unit 270 is realized by a combinational circuit and has a register 271. Further, the control unit 270 exchanges data between the ADC 151A and the level shifter 280. The control unit 270 operates according to the content of the command based on the command input from the terminal 152A via the level shifter 280.

When the control unit 270 receives a command indicating the start of measurement of the digital biological signal from the MPU 150B, the control unit 270 outputs a start signal for starting the digital conversion process to the ADC 151A to the ADC 151A and outputs a CS signal to the MPU 150B. Further, when the biological signal acquisition process is performed, the control unit 270 causes the clock generator 250 to output the clock for AD conversion synchronization, and outputs the clock for AD conversion synchronization to the MPU 150B. The clock for synchronizing the start signal, the CS signal, and the AD conversion is synchronized with the system clock of the ASIC150A. Here, as an example, the clock for synchronization of AD conversion and the system clock are both 4 MHz clocks, which are the same clocks.

The start signal is output from the register 271 to the ADC 151A only once when the ADC 151A starts the digital conversion process. More specifically, when the ADC 151A starts the digital conversion process, an H level pulse is output from the register 271 to the ADC 151A only once.

The CS signal is output from the control unit 270 to the MPU 150B from the terminal 152A via the level shifter 280. The CS signal is a signal output by the control unit 270 to the MPU 150B. The CS signal is a synchronization signal for causing the MPU 150B to acquire a digital biological signal.

The clock for synchronization of the AD conversion is a clock for synchronization used by the ADC 151A when performing the AD conversion, and is output from the clock generator 250 to the ADC 151A. The ADC 151A performs AD conversion when the clock for synchronizing AD conversion rises to the H level.

The ADC 151A performs AD conversion in synchronization with the AD conversion synchronization clock output from the clock generator 250, and the MPU 150B is digital at the timing when the CS signal switches from the H (High) level to the L (Low) level. Capture biological signals. Therefore, the digital conversion process in the ADC 151A and the data acquisition in the MPU 150B can be synchronized. The frequency of the CS signal is, for example, 2 to 8 times higher than the frequency of the system clock on the ASIC150A side.

Further, the control unit 270 outputs the digital biological signal output from the ADC 151A to the level shifter 280 while performing the biological signal acquisition process. The digital biological signal is output from the level shifter 280 to the MPU 150B via the terminal 152A. Further, the control unit 270 exchanges other commands and data with the MPU 150B via the level shifter 280 and the terminal 152A.

The register 271 is a data holding unit that holds a digital biological signal output from the ADC 151A, a start signal output from the control unit 270 to the ADC 151A, a CS signal, and the like.

The level shifter 280 adjusts the signal level of data, commands, etc. between the control unit 270 and the terminal 152A.

FIG. 6 is a timing chart showing the processing of the MPU 150B. FIG. 6 (A) shows the timing when the comparison MPU acquires the data x _{0 to} x ₇ and then performs the addition process and the averaging process, and FIG. 6 (B) shows the timing when the MPU 150B performs the data x _0. The timings of the addition process performed each time ~ x ₇ is acquired and the averaging process performed on the added value of the data x _{0 to} x ₇ are shown.

Here, the data x _{0 to} x ₇ are digital biological signals, and the horizontal axis in FIGS. 6 (A) and 6 (B) represents time.

As shown in FIG. 6A, the comparison MPU acquires data x ₀ to x ₇ in order according to the system clock. The lengths of the periods T _{0 to} T ₇ required to obtain each of the data x _{0 to} x ₇ are equal to each other. The period Tsa between the periods T _{0 to} T ₇ is a period during which the acquired data is transferred to the memory. When the MPU for comparison acquires the data 8 and transfers it to the memory, the data x ₀ to x ₇ is read from the memory in the period TA, and the added value A of the data x ₀ to x ₇ is obtained according to the following equation (1). Further obtain the average value (A / 8) of the added value A.

When the MPU for comparison obtains the average value (A / 8) of the added value A, the process is restarted from the acquisition of the data x ₀ , and the process shown in FIG. 6 (A) is repeatedly executed.

As shown in FIG. 6 (B), the MPU 150B acquires each of the data x ₀ to x ₇ from the ASIC 150A when the CS signal changes from the H level to the L level at the start of the period T _{0 to} T ₇ , and the data x _0. Every time each of ~ x ₇ is acquired, addition processing is performed according to the following equation (2) in the period Tsb. In addition processing is added to the previous sum value A _n every time the data x ₀ ~x ₇ is obtained.

However, A ₀ = 0, n = 0, 1, 2, ..., 7.

In the eight periods Tsb after acquiring the data x _{0 to} x ₇ , the added values A _{1 to} A ₈ are obtained, respectively. The added value A ₈ is a value obtained by adding the data x _{0 to} x ₇ . Since the start of the period TB is the start of the next period T ₀ , the MPU 150B acquires data x ₀ from the ASIC 150A when the CS signal changes from the H level to the L level at the start of the period T ₀ .

MPU150B, when obtaining the addition value _{A 8} acquires data 8, the average value of the sum _{A 8 (A} 8/8) in the next period TB.

In this way, the MPU 150B performs an addition process of adding according to the equation (2) in eight periods Tsb after acquiring the data x _{0 to} x ₇ . Here, the period Tsb of FIG. 6 (B) and the period Tsa of FIG. 6 (A) are both times for leaving a space between tasks so that interrupt processing can be performed when the MPU 150B processes in the background. .. Therefore, the period Tsb in FIG. 6 (B) and the period Tsa in FIG. 6 (A) are substantially equal to each other.

Then, in the next period TB of the period _{T 7} of obtaining the addition value _{A 8,} since it is only determined average value of the sum _{A 8} a _(A 8/8), compared with the period TA shown in FIG. 6 (A) Therefore, the period TB can be significantly shortened.

Simulation of the power consumption when the sticky biosensor including the MPU for comparison performs the process shown in FIG. 6 (A) and the power consumption when the sticky biosensor 100 performs the process shown in FIG. 6 (B). It was found that it can be reduced from 6.1 mA to 5.8 mA.

This means that, for example, when the same battery 160 is used for the sticky biosensor including the MPU for comparison and the sticky biosensor 100, the continuous usable time is extended from about 33 hours to about 40 hours. Equivalent to. Since the stick-on biosensor 100 consumes less power than the stick-on biosensor including the comparison MPU, the result is that the continuous usable time is extended by about 20%.

If the average value of the sum _{A 8 (A} 8/8) is obtained as described above, the main control unit 151B of the MPU150B is stored and transferred average value of the sum _{A 8} a _(A 8/8) in the memory 150C To do. The reason for performing the addition averaging process in this way is to reduce the noise level of the digital biological signal (to improve the S / N ratio).

FIG. 7 is a flowchart showing the processing of the MPU 150B using electrocardiographic data as an example of a biological signal. The flowchart of FIG. 7 is a process from the start to the end of recording of digital electrocardiographic data by the MPU 150B, which is repeatedly executed over 24 hours as an example.

When the process starts, the main control unit 151B outputs a command to start the ECIC data acquisition process to the ASIC 150A (step S1). The ASIC 150A causes the ADC 151A to start the digital conversion process.

The calculation unit 153B sets n = 0 (step S2).

The calculation unit 153B takes in digital electrocardiographic data from the ASIC 150A according to the CS signal (step S3).

The calculation unit 153B performs the addition process according to the equation (2) (step S4).

The calculation unit 153B determines whether n is 7 or more (step S5).

When the calculation unit 153B determines that n is not 7 or more (S5: NO), n is incremented (step S6).

Calculation unit 153B is n is 7 or more in the step S5 (S5: YES) and it is determined, the average value of the sum _{A 8} a _(A 8/8) determining (step S7).

Calculation unit 153B stores the average value _(A 8/8) in the memory 150C (step S8).

The main control unit 151B determines whether or not 24 hours have passed since the recording of the digital electrocardiographic data was started (step S9).

When the main control unit 151B determines that 24 hours have not passed (S9: NO), the main control unit 151B returns the flow to step S2.

On the other hand, when it is determined that 24 hours have passed (S9: YES), the main control unit 151B transmits a command to end the electrocardiographic data acquisition process to the ASIC 150A (step S10). The ASIC 150A terminates the digital conversion process on the ADC 151A. Therefore, the ADC 150A continues to perform the digital conversion process from receiving the command for starting the electrocardiographic data acquisition process until receiving the command for ending the electrocardiographic data acquisition process. The MPU 150B obtains the average value of the digital electrocardiographic data from the transmission of the command to start the electrocardiographic data acquisition process to the ASIC 150A to the transmission of the command to end the electrocardiographic data acquisition process to the ASIC 150A, and obtains the average value of the digital electrocardiographic data, and the memory 150C Continues the process of storing in.

By the above-mentioned processing, the total value of the digital electrocardiographic data is obtained over 24 hours, the averaging processing is performed, and the data is stored in the memory 150C.

As described above, in the embodiment, the ASIC 150A performs, for example, an electrocardiographic data acquisition process as a biological signal, acquires analog electrocardiographic data, and digitally converts it into digital electrocardiographic data. The MPU 150B mainly performs an addition process (step S4) of digital electrocardiographic data output from the ASIC 150A, an average value acquisition process (step S7), and a process of storing the average value in the memory 150C (step S8). ..

In this way, since the ASIC 150A performs the process of acquiring the analog biological signal and the digital conversion process, the arithmetic processing capacity of the MPU 150B does not have to be so high. In addition, ASIC150A is overwhelmingly cheaper than MPU150B.

Therefore, it is possible to provide a stick-on biosensor 100 suitable for a disposable type. Disposable means to use it only once without using it repeatedly. The user of the stick-on biosensor 100 discards the stick-on biosensor 100 after finishing the measurement of the electrocardiographic waveform.

Further, from an economical point of view, the suitable for the disposable type means that the electrocardiographic waveform acquired by the user of the stickable biosensor 100 is obtained under the precondition that the sticky biosensor 100 is used only once. It means that the data to be represented can be passed to a medical institution to obtain the diagnosis result of the doctor's diagnosis, and the company that provides the obtained diagnosis result to the user can produce it at a sufficiently payable amount by the usage fee paid by the user. ..

In addition, the fact that it is suitable for the disposable type means that it does not require a difficult disassembly process in terms of configuration, and can be made ready for disposal by, for example, a disassembly process that is easy and safe for the user to remove the battery 160. Say. The stick-on biosensor 100 is configured so that the battery 160 can be easily removed by peeling the cover 170 from the base material layer 120.

Further, in the stick-on biosensor 100, after the addition processing is performed according to the equation (2) in the eight periods Tsb after the data x _{0 to} x ₇ are acquired, the addition value A ₈ of the data x _{0 to} x ₇ is obtained. in the period TB of, for only determining the average value of the sum a ₈ a (a _8/8), can reduce the processing time for obtaining the average value of the sum, it is possible to reduce power consumption.

Also, sticking type biometric sensor 100, MPU150B is determined an addition value _{A n + 1} shown in FIG. 6 (B), while seeking the average value of the sum _{A 8} a _(A 8/8), the system clock of MPU150B The frequency is reduced to 4 MHz, which is equal to the sampling frequency of the ADC 151A. This also makes it possible to reduce power consumption.

In the above, the mode in which the MPU 150B has eight additional value data when calculating the average value of the added values has been described, but the number of added value data when calculating the average value of the added values is two or more. Any number may be used.

Although the stick-on biosensor of the exemplary embodiment of the present invention has been described above, the present invention is not limited to the specifically disclosed embodiment and deviates from the scope of claims. It is possible to make various modifications and changes.

100 Stick-on biosensor 110 Pressure-sensitive adhesive layer 120 Base material layer 130 Circuit part 140 Probe 150 Electronic device 150A ASIC
150B MPU
150C memory 150D, 150E bus 151A ADC
151B Main control unit 152B Switching setting unit 153B Calculation unit 154B Memory 160 Battery

Claims (3)

A pressure-sensitive adhesive layer with a sticking surface that can be stuck to the subject,
The electrodes that come into contact with the subject and
A base material layer provided on the opposite surface of the pressure-sensitive adhesive layer to which it is attached,
An electronic device provided on the base material layer, having an integrated circuit and an information processing device, and processing analog data acquired via the electrodes.
A circuit unit provided on the base material layer and connecting the electrode and the electronic device is included.
The integrated circuit has a first input terminal connected to the electrode, an A / D converter that converts analog data input via the first input terminal into digital data, and an output terminal.
The information processing device has a second input terminal connected to the output terminal.
The control unit of the integrated circuit is a stick-on biosensor that outputs the digital data from the output terminal to the information processing device. Further including a memory connected to the information processing device,
The stick-on biosensor according to claim 1, wherein the information processing device obtains an average value of digital data acquired by the integrated circuit over a predetermined number of times and stores the average value in the memory. The stick-on biosensor according to claim 2, wherein the information processing device obtains the sum of digital data acquired by the integrated circuit over a predetermined number of times, and obtains the average value of the sum as the average value.

Images