JP5984645B2 - Pressure sensor and pressure sensor device - Google Patents

Description

  The present invention relates to a conductor using a conductive polymer and a binder resin, a method for producing the conductor, a pressure sensor using the conductor, a pressure sensor device including the pressure sensor, and the conductor. The present invention relates to a bioelectrode used and a biosignal measurement apparatus including the bioelectrode.

  In an aging society, there is an increasing need to continuously measure biological signals such as electrocardiogram monitoring over a long period of time. In addition, prevention and early detection of pressure ulcers (bed slippage) in patients who have been bedridden for a long time in medical institutions and nursing homes are a major issue, and the introduction of pressure sensors is being considered as one of the solutions. Yes. Pressure sensors are attracting attention not only for medical purposes but also as functional wear functions in the field of health sports. For example, there is a growing need for pressure sensitive sensors that measure the impact of landings when running or jumping. Further, in the ITC field, improvement of an interface for operating a touch pad or a cursor as an input device is required. In order to meet these needs, not only the physical characteristics of the sensor but also the high quality of the interface including the feeling of wearing is required. For example, it is expected to realize a flexible fiber or cloth sensor that does not feel uncomfortable even if the sensor is installed on clothing such as underwear, gloves, and socks.

  As an existing pressure sensor, a strain gauge type pressure transducer is generally used. This is a device for electrically measuring deformation of a flexible substrate as a main body, and its basic shape is a flat plate (panel). Since it is a flat plate having rigidity, there is a problem in conformity of the shape when it is installed on a limb or fingertip. That is, it is difficult to obtain a shape that matches the curve of the skin or clothes, and there is a difference between the installation surface and the device, making it uncomfortable to wear. As a solution to this problem, flexible sensors using various polymer polymers and sheet sensors using conductive rubber have been proposed. However, these conventional sensors have poor breathability, are hydrophobic, and have problems such as stuffiness due to sweating.

  In recent years, a sheet-like sensor using conductive fibers has been proposed, and its practical application has been studied as a technique for measuring the pressure applied when a person lies on a bed or the like. Patent Document 1 discloses a sheet-like sensor configured by using a yarn in which conductive fibers are covered with an insulating material and made of a fabric of the yarn. In this sensor, the pressure change at the intersection of the warp and the weft constituting the fabric is detected as a change in the capacitance of the capacitor formed between the warp and the weft. At this time, since the number of intersecting portions is extremely large, the detection circuit becomes complicated and the circuit needs to be adjusted. Further, there is a problem that the structure of the yarn itself constituting the woven fabric is a complicated structure in which a metal fiber is a core and cotton or polyester fiber is wound around the metal fiber.

JP 2006-234716 A

  The present invention has been made in view of the above circumstances, and can be used as a member of a pressure-sensitive sensor or a bioelectrode, has a simple structure and can be easily manufactured, a method for manufacturing the conductor, and the conductor It is an object of the present invention to provide a pressure-sensitive sensor and a biological electrode using a pressure sensor, a pressure-sensitive sensor device including the pressure-sensitive sensor, and a biological signal measuring device including the biological electrode.

  The inventors of the present invention have a high hydrophilicity and flexibility of a fiber (thread) made of a conductive polymer typified by PEDOT-PSS. On the other hand, when the fiber comes into contact with sweating skin, the fiber is structurally As a result of repeated research on the problem of collapse, the present invention was completed. The present invention provides the following solutions.

(1) A conductor comprising a mixture containing a conductive polymer and a binder resin coated on a fiber or fabric is used for a pressure sensitive sensor of the following (2) .

  According to the conductor described in (1) above, the conductive polymer is kneaded in the solidified (cured) binder resin (polymer) and coated on the fiber or fabric, so sweating occurs. Even in a moist environment such as the skin, the structural breakdown of the conductor hardly occurs, and high conductivity can be maintained for a long period of time. Moreover, a flexible conductor can be formed by taking advantage of the inherent flexibility of the fiber or fabric. Despite the state in which the conductive polymer is kneaded into the binder resin, the conductivity of the conductive polymer is so high that it can be used practically without any problem, and hardly deteriorates. For this reason, when the conductor is applied to a biological electrode or a pressure sensor, the conductive polymer contained in the solidified binder resin can detect a weak electrical signal of the living body or change of the weak electrical signal due to a pressure change. Therefore, high-sensitivity and high-accuracy signals can be transmitted and received between the external device and the biological electrode or pressure sensor. Furthermore, since the mechanical strength of the conductor is enhanced by the solidified binder resin, the conductor is not easily damaged by an external force and excellent in durability when the bioelectrode and the pressure sensor are attached.

(2) A bioelectrode characterized by using the conductor according to (1) can be exemplified as a related invention .

The conductor (1) can be used for producing a bioelectrode. According to prior Symbol bioelectrode, by a fibrous (filamentous) or cloth-like conductor showing a uniform conductivity is placed on the living body surface, the conductive polymer contained in the conductive body weak electrical in vivo A signal can be detected. Furthermore, the binder resin constituting the conductor has improved durability such as mechanical strength, chemical resistance, water resistance, abrasion resistance, peel resistance, heat resistance, etc., in a moist environment such as sweating skin. Also function stably over a long period of time. In addition, since it is possible to maintain the original flexibility, air permeability, and water absorption of the fibers or fabrics constituting the conductor, the bioelectrode mounting property is remarkably improved. Since the bioelectrode of the present invention has a simple conductor structure, it can be easily produced at low cost.

(3) The conductor according to the above (1), that is, a cloth body constituted by a conductor in which a mixture containing a hydrophilic conductive polymer and a binder resin is coated on a fiber or cloth; the side by side so as to contact both sides of the conductive surface of the fabric body is arranged, comprising a plurality of conductive linear member made of a fiber coated with a conductive polymer having a hydrophilic, wherein the conductive surface The plurality of members arranged in parallel on the front surface of the conductive surface are arranged so as to be substantially orthogonal to the plurality of members arranged in parallel on the back surface of the conductive surface. Pressure sensor to be used.

According to the pressure-sensitive sensor as described in (3) above, the pressure applied to the sensor is controlled so that the mixture containing the hydrophilic conductive polymer and the binder resin is coated on the fiber or fabric. A plurality of conductive fibers composed of fibers coated with a hydrophilic conductive polymer that is absorbed on the cloth body (cloth-like conductor) shown in FIG. to measure derives from the linear member, together with the exhibit conventional pressure sensitive stable pressure sensitive properties than the sensor, the original flexibility fabric constituting the fabric body, also possible to maintain the breathability or water absorption Therefore, the mounting property of the pressure-sensitive sensor is remarkably improved as compared with the conventional flat plate-shaped pressure-sensitive sensor. Further, the resistance value (capacitance) of the cloth body can be adjusted by the amount of the conductive polymer contained in the mixture coated on the cloth body (cloth-like conductor), and functions by a simple peripheral circuit. Can give the electrical characteristics. For example, the pressure-sensitive sensor of the present invention can be made to function by being directly connected to an AD converter mounted on a general microcomputer chip. Since the structure of the cloth body is particularly simple, the pressure sensitive sensor of the present invention can be easily produced at low cost. The cloth body can also function as a biological electrode, and the pressure-sensitive sensor of the present invention can also function as a biological electrode.

(4) A pressure- sensitive sensor device comprising: the pressure-sensitive sensor according to (3); and an external device that is connected to the pressure-sensitive sensor and transmits and receives signals to and from the pressure-sensitive sensor. .

  The pressure-sensitive sensor included in the pressure-sensitive sensor device according to the above (4) includes a conductor having excellent durability and exhibits stable pressure-sensitive characteristics. Therefore, the pressure-sensitive sensor includes an external device connected to the pressure-sensitive sensor. In the meantime, transmission and reception of signals can be stably performed with high sensitivity and high accuracy over a long period of time. Further, since the mounting property of the pressure sensor is improved, a wearable pressure sensor device can be realized by downsizing the external device.

(5) A resin composition containing a conductive polymer and at least one of a binder resin or a polymerizable compound constituting the binder resin is attached to a fiber or fabric, and the resin composition is solidified or polymerized. By making it, the manufacturing method of the conductor characterized by coating the said fiber or fabric can be illustrated as a related invention .

  According to the method for producing a conductor described in (5) above, a conductor having a simple structure excellent in strength can be produced. By selecting the binder resin or the type of polymerizable compound constituting the binder resin according to the purpose, the durability such as mechanical strength, chemical resistance, water resistance, abrasion resistance, peel resistance, heat resistance, etc. An excellent conductor can be easily manufactured.

(6) A conductor characterized in that a mixture containing a conductive polymer and a binder resin is coated on the surface of a thermal transfer sheet can be exemplified as a related invention .

  According to the conductor described in (6), the conductive polymer is coated on the surface of the thermal transfer sheet in a state of being kneaded in the solidified (cured) binder resin (polymer). By heating the conductor with a heating tool such as an iron, the conductive polymer kneaded in the binder resin can be transferred to the substrate together with the thermal transfer sheet. Since the conductive surface of the transferred conductor is reinforced with a binder resin and a thermal transfer sheet, even in a moist environment such as sweating skin, the conductor is unlikely to collapse structurally and has high conductivity over a long period of time. Can be maintained. Moreover, when the base material to be transferred is a fabric, a flexible conductor can be formed by utilizing the inherent flexibility of the fabric. Despite the state in which the conductive polymer is kneaded into the solidified binder resin, the conductivity of the conductive polymer is so high that it can be used practically without any deterioration. For this reason, when the conductor is applied to a biological electrode, the conductive polymer contained in the solidified binder resin can detect a weak electrical signal of the living body. And between the bioelectrode and the bioelectrode. Furthermore, since the mechanical strength of the conductor is enhanced by the solidified binder resin, the conductor is not easily damaged by an external force in the state where the bioelectrode is attached, and the durability is excellent.

(7) A bioelectrode in which the conductor is thermally transferred to a substrate so that the surface coated with the conductor according to (6) is exposed can be exemplified as a related invention. .

  According to the biological electrode as described in (7) above, the conductive polymer contained in the coating surface is a weak electrical signal of the living body by installing the coating surface exposed to the outside showing uniform conductivity on the biological surface. Can be detected. In addition, the binder resin that forms the coating surface has improved durability such as mechanical strength, chemical resistance, water resistance, abrasion resistance, peel resistance, and heat resistance. Also function stably over a long period of time. In addition, when the substrate on which the conductor has been thermally transferred is a fabric, it is possible to maintain the inherent flexibility, breathability, or water absorption of the fabric, so that the wearability of the bioelectrode is significantly improved. ing. Since the bioelectrode of the present invention has a simple conductor structure, it can be easily produced at low cost.

(8) A biological signal measuring device including the biological electrode according to (2) or (7) can be exemplified as a related invention .

  The biological electrode provided in the biological signal measuring device according to (8) above has a conductive body (conductive surface) with excellent durability and can detect weak biological signals from the biological surface. Thus, it is possible to stably transmit and receive signals to and from the external device over a long period of time with high sensitivity and high accuracy. Furthermore, since the wearability of the bioelectrode is improved, a wearable biosignal measuring device can be realized by downsizing the external device.

  According to the conductor of the present invention, it is possible to provide conductive fibers (threads) and conductive cloths (conductive cloth bodies) excellent in durability.

  The bioelectrode of the present invention functions stably over a long period even in a moist environment such as sweating skin. In addition, the wearability of the bioelectrode is remarkably improved. Furthermore, since the structure of the conductor constituting the bioelectrode is simple, the bioelectrode can be easily produced at low cost.

The pressure-sensitive sensor of the present invention comprises a fiber coated with a hydrophilic conductive polymer disposed on both sides of a change in electrical characteristics accompanying deformation of a cloth-like conductor (cloth body). to measure derives from electrodes constituted by a plurality of conductive linear member, together with the exhibit a stable pressure-sensitive characteristics, it is operable with a simple peripheral circuit. In addition, the wearability of the pressure sensor is greatly improved. Furthermore, it can have a function as a bioelectrode.

  According to the method for producing a conductor of the present invention, a mixture containing a conductive polymer kneaded in a binder resin is adhered to an arbitrary base material in an arbitrary form (pattern). Can be easily manufactured. Moreover, the said conductor can be manufactured in the state which maintained the characteristics, such as a softness | flexibility, air permeability, and water absorption which the fiber or fabric which comprises a base material originally has. Furthermore, since the manufacturing method is easy, the conductor can be easily produced at low cost.

According to the pressure-sensitive sensor device of the present invention, the wearability of the pressure-sensitive sensor provided in the pressure-sensitive sensor device is improved. Therefore, the wearable pressure-sensitive sensor device is reduced by downsizing the external connection device. Can be realized.
According to the biological signal measuring device of the present invention, the wearability of the biological electrode provided in the biological signal measuring device is improved. Therefore, the wearable biological signal measuring device is reduced by downsizing the external connection device. Can be realized.

(A) is a photograph showing a state in which conductors constituting a bioelectrode are installed at two locations on the front chest and upper arm of a T-shirt. (B) is a schematic diagram showing a schematic configuration of a biological electrode. (C) is the result of measuring an electrocardiogram of an adult male using a bioelectrode. It is the schematic which shows an example of the method of installing a conductor in the cloth of a T-shirt. It is the schematic which shows another example of the method of installing a conductor in the cloth of a T-shirt. It is a schematic diagram which shows schematic structure of a pressure sensor. It is a graph which shows the relationship between a pressure and an electrical resistance in the pressure sensor used for the measurement.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings, but the present invention is not limited to such embodiments.

"conductor"
<First embodiment>
The conductor according to the first embodiment of the present invention is formed by coating a fiber or fabric with a mixture containing a conductive polymer and a binder resin.

  The kind in particular of said conductive polymer is not restrict | limited, A conventionally well-known conductive polymer is applicable. For example, PEDOT-PSS, PEDOT-S etc. which are excellent in electroconductivity and hydrophilicity are mentioned. By using a conductive polymer having excellent hydrophilicity, the hydrophilicity of the conductive portion of the conductor of the present invention can be increased. A conductor having a highly hydrophilic conductive site has a high affinity for the skin, and thus is suitable for use in bioelectrodes and pressure sensors described later.

  PEDOT-PSS is a conductive polymer obtained by polymerizing 3,4-ethylenedioxythiophene as a monomer in the presence of poly (4-styrenesulfonic acid). PSS functions as a dopant that imparts a negative charge to PEDOT. From the viewpoint of increasing the conductivity of the conductive polymer, the conductive polymer preferably contains a dopant.

  A conductor obtained by solidifying PEDOT-PSS alone gels in a relatively wet environment such as sweating skin due to the high water absorption of PEDOT-PSS, and the mechanical strength is extremely reduced. For this reason, it is difficult to install a conductor made of PEDOT-PSS processed into a rod shape or a plate shape alone on the skin surface and use it for a long period of time.

  The conductor of the first embodiment is a fiber or fabric obtained by mixing a resin composition in which a conductive polymer, a binder resin as an adhesive material and / or a monomer of the binder resin, and a solvent to be added as necessary are mixed. It is a conductor that is attached to a base material made by coating, printing, dipping, spraying, dropping, or the like, and further solidified or polymerized by drying, heating, heating, or the like. In this conductor, the conductive polymer contained in the solidified resin composition (mixture) is kneaded into the binder resin, solidified, and further supported by the base material, which is excellent in durability.

The type of the binder resin is not particularly limited as long as it is a binder resin capable of adhering (binding) the conductive polymer to the fiber or the fabric without deactivating the conductivity of the conductive polymer. Conventionally known binder resins can be applied.
One kind of binder resin may be used alone, or two or more kinds may be used in combination. By combining two or more kinds, the curability, adhesiveness (tackiness), and ease of handling (workability such as coating) of the binder resin may be improved.

Examples of the binder resin include thermoplastic resins, thermosetting resins, and photocurable resins. For example, Nafion, polycarbonate, polyacrylonitrile, polyethylene, polypropylene, polybutene, polyether, polyester, polystyrene, poly-p -Thermoplastic resins including thermoplastic elastomers such as xylene, polyvinyl acetate, polyacrylate, polymethacrylate, polyvinyl chloride, polyvinylidene chloride, polyvinyl ether, polyvinyl ketone, polyamide, butadiene resin, fluorine resin, polyurethane resin , Urea resin, melamine resin, modified silicone resin, phthalic acid resin, phenol resin, furan resin, aniline resin, unsaturated polyester resin, xylene / formaldehyde resin, epoxy resin, etc. RESIN, epoxy acrylate, acrylic epoxy cationic polymerization, and the like photocurable resin such as photosensitive polyimide.
Of these, the various vinyl resins, Nafion, polyamide, polyethylene, polypropylene, phthalic acid resin, modified silicone resin, and acrylic resin are preferable.

In particular, an acrylic resin is most preferable as a binder resin because it has high adhesion to a substrate (fiber) and is not easily peeled off from the substrate. Furthermore, the acrylic resin is easy to adjust the tackiness, has high processability, and imparts flexibility with additives, and is relatively easy to bond and cure. It is particularly suitable for applications that bind between fibers.
On the other hand, polyvinyl alcohol (hereinafter PVA) is not necessarily a good material for the binder resin. PVA is not suitable because it has a lower adhesive force than acrylic resins and easily peels. Also, when PVA acetalization or curing treatment with a cross-linking agent is added to reduce peeling, the strength of the PVA polymer will be improved, but the adhered substrate (fiber) will become harder, giving it flexibility and tactile sensation. Getting worse. For this reason, it is not suitable to use PVA as a binder resin as a bioelectrode material that requires flexibility in direct contact with the skin.

  When an unpolymerized monomer that is a precursor of a binder resin is contained in the resin composition when the conductor according to the first embodiment is manufactured, an unpolymerized monomer is present in the mixture after polymerization (after solidification). It may remain. The monomer in the resin composition may be positively polymerized by being attached to the substrate and then heated (thermosetting), light irradiation (photocuring), addition of a polymerization accelerator, etc. It may be polymerized gently and spontaneously by drying, heating, contact with air, or the like.

  When manufacturing the conductor of the first embodiment, a resin (polymer) polymerized in advance may be contained in the resin composition as the binder resin.

  Preferable specific examples of the binder resin include polymers obtained by polymerizing the monomers exemplified below. Examples of the acrylic monomer include (meth) acrylic acid, methyl (meth) acrylate, ethyl (meth) acrylate, n-butyl (meth) acrylate, t-butyl (meth) acrylate, isobutyl (meth) acrylate, hexyl (meth) ) Acrylate, octyl (meth) acrylate, cyclohexyl (meth) acrylate, tetrahydrofurfuryl (meth) acrylate, 2-hydroxymethyl (meth) acrylate, 2-hydroxyethyl (meth) acrylate, 2-hydroxypropyl (meth) acrylate, 2-ethylhexyl (meth) acrylate, stearyl (meth) acrylate, lauryl (meth) acrylate, methoxypolyethylene glycol # 400 (meth) acrylate, methoxypolyethylene glycol # 1000 (meth) ) Acrylate, methoxypolyethylene glycol # 2000 (meth) acrylate, glycidyl (meth) acrylate, (meth) acrylamide, methyl (meth) acrylamide, ethyl (meth) acrylamide, propyl (meth) acrylamide, isopropyl (meth) acrylamide, butyl ( (Meth) acrylamide, diacetone (meth) acrylamide, N-methylol (meth) acrylamide, N-hydroxyethyl (meth) acrylamide, N-hydroxypropyl (meth) acrylamide, N-hydroxybutyl (meth) acrylamide, N-methoxymethyl ( Examples include meth) acrylamide, N-ethoxymethyl (meth) acrylamide, N-butoxymethyl (meth) acrylamide, and N-isobutoxymethyl (meth) acrylamide.

  By using these acrylic resins as binder resins, the mixture can be securely fixed to a substrate made of fibers or fabrics, and the abrasion resistance, peel resistance, water resistance, chemical resistance and mechanical strength of the mixture can be improved. While being able to improve more, the electroconductivity of the conductive polymer embedded in the acrylic resin can be maintained easily.

  Furthermore, depending on the blending ratio of the conductive polymer and the acrylic resin in the mixture, the hydrophilicity and flexibility of the conductive polymer embedded in the acrylic resin are maintained, and the mixture contains these The nature is reflected to some extent. Hydrophilicity and flexibility are properties required as preferable characteristics of the bioelectrode described later. As a mechanism for maintaining the properties of the conductive polymer even after being embedded in the acrylic resin, the contact between the conductive polymers is maintained even in the embedded state, and further, the surface of the mixture has a high conductivity. This is probably because at least a part of the molecule is exposed.

  The content of the conductive polymer in the mixture is not particularly limited as long as the mixture maintains conductivity, but is preferably 0.1 to 50% by weight, and more preferably 1 to 40% by weight. 10 to 30% by weight is preferable. The electroconductivity of a mixture improves further that it is more than the lower limit of the said range (0.1-50 weight%). When the amount is not more than the upper limit of the above range, the balance of the content of the conductive polymer with respect to the binder resin is further improved, and the durability of the mixture is further improved.

  The content of the binder resin in the mixture is not particularly limited as long as the mixture maintains conductivity, but is preferably 50 to 99.9% by weight, more preferably 60 to 99% by weight, More preferably, it is 70 to 90% by weight. When the amount is not less than the lower limit of the above range (50 to 99.9% by weight), the balance of the binder resin content with respect to the conductive polymer becomes better, and the durability of the mixture is further improved. When the amount is not more than the upper limit of the above range, the conductivity of the mixture is further improved.

  The total content of the conductive polymer and the binder resin in the mixture is not particularly limited as long as the mixture maintains conductivity, but is preferably 50 to 100% by weight, for example, 60 to 100% by weight. % Is more preferable, and 80 to 100% by weight is still more preferable. When the content is in the above range (50 to 100% by weight), the balance between the content of the conductive polymer and the binder resin becomes better, and the durability and conductivity of the mixture are further improved.

  The weight ratio of the conductive polymer and the binder resin in the mixture is not particularly limited as long as the mixture maintains conductivity, but for example, binder resin / conductive polymer = 1 to 100 is preferable. 2-10 are more preferable, 4-10 are still more preferable, and 4-6 are especially preferable. Within the above range (4 to 10), the balance between the content of the conductive polymer and the binder resin becomes better, and the durability and conductivity of the mixture are further improved.

  The fiber or fabric constituting the conductor of the first embodiment is not particularly limited as long as it can function as a base material that supports the mixture, and fibers or fabrics used in conventionally known clothes and the like are used. Applicable. The fabric is not limited to a woven fabric and may be a non-woven fabric.

  When the base material of the conductor of the first embodiment is a fiber, the conductor is a conductive fiber. When the base material of the conductor of the first embodiment is a fabric, the conductor is a conductive cloth. The conductive fiber may be used as an electrical wiring or a one-dimensional (string-like) biological electrode, or may be used as a conductive cloth by weaving conductive fibers. The conductive cloth can be used as a two-dimensional bioelectrode.

  The phrase “the fiber or fabric is coated” means that at least a part of the fiber is covered with the mixture, or the mixture is attached to at least one region of the fabric. The mixture coated on the fabric may be attached to the surface (front surface) and / or the back surface of the fabric, and the fibers are bound between the fibers (threads) constituting the fabric. You may adhere to wear. When the mixture is coated on both surfaces of the fabric, the conductive surface made of the mixture on the front surface and the conductive surface made of the mixture on the back surface may be electrically independent or electrically conductive. You may do it. Further, a part of the mixture may penetrate into the fiber.

<Second embodiment>
The conductor of the second embodiment of the present invention is obtained by coating the surface of a thermal transfer sheet with a mixture containing a conductive polymer and a binder resin.

  The description of the mixture, and the conductive polymer and the binder resin constituting the mixture are the same as the description of the first embodiment, and will be omitted.

The configuration of the thermal transfer sheet is not particularly limited as long as it has a thermoplastic resin layer and a layer made of the mixture can be laminated on the surface of the thermoplastic resin layer. The thermal transfer sheet may be composed only of a thermoplastic resin layer.
Another configuration of the thermal transfer sheet includes a configuration having a sheet base material and a thermoplastic resin layer laminated (coated) on the sheet base material. The sheet base material is not particularly limited as long as it can support the thermoplastic resin layer and does not depart from the gist of the present invention.

  The thermoplastic resin constituting the thermoplastic resin layer is preferably a resin that exhibits adhesiveness (adhesiveness) when heated at a temperature that does not damage the mixture. For example, a thermoplastic resin having a glass transition point or melting point of 80 to 200 ° C. is preferable. Specific examples include ethylene-vinyl acetate copolymer, polyvinyl acetate, polyvinyl chloride, polyethylene, polystyrene, polypropylene, and polyethylene terephthalate.

  By using the conductor according to the second embodiment, for example, a household iron can be used to install the mixture having conductivity on existing clothes and the like. As an application example thereof, a biological electrode described below can be cited.

<< Biological electrode; Third embodiment >>
The bioelectrode of the third embodiment of the present invention uses the conductor of the present invention. A biological signal such as an electrocardiogram or an electroencephalogram can be detected by installing a conductor constituting the biological electrode on a biological surface such as skin.

  An example of the biological electrode 10 of the third embodiment is shown in FIG. FIG. 1A is a photograph showing a state in which the bioelectrode conductor 1 is installed at two locations on the front chest and upper arm of the T-shirt 2. An electrocardiograph 3 is connected to each conductor 1 via wiring. FIG. 1B is a schematic diagram showing a schematic configuration of the biological electrode 10. A thermal transfer sheet 6 composed only of a thermoplastic resin layer is thermally fused to the fabric of the T-shirt 2, and a conductive mixture 4 is laminated on the thermal transfer sheet 6. A conductive nylon thread 5 (silver-coated nylon thread 5) coated with silver is sewn on the conductive surface made of the mixture 4, and its extension is drawn out of the conductive surface as a wiring. . Furthermore, the extension constituting the wiring is covered with a thermal transfer sheet 6 made of a thermosetting resin layer, and is sandwiched between the fabric of the T-shirt 2 and the thermal transfer sheet 6 and electrically insulated. FIG. 1C shows the result of measuring an electrocardiogram of an adult male using the bioelectrode 10. The horizontal axis represents time (time), and the vertical axis represents the heart rate per minute.

  FIG. 2A shows an example of a method for installing the conductor 1 on the fabric of the T-shirt 2. (1) is a schematic cross-sectional view of commercially available iron print paper. A thermoplastic resin layer 6 is disposed on the mount 8. (2) is a schematic cross-sectional view in which the layer of the mixture 4 formed by applying the resin composition on the thermoplastic resin layer 6 and then solidifying it is laminated. (3) and (4) show a state in which the thermoplastic resin layer 6 is peeled off from the mount 8 and inverted, and the layer of the mixture 4 is applied to the mount 8 and temporarily fixed. (5) The thermoplastic resin layer 6 and the layer of the mixture 4 are applied to the T-shirt 2 by applying the thermoplastic resin layer 6 to the fabric of the T-shirt 2 and applying a household iron from the mount 8 to heat. It shows how it is transferred to the fabric. The layer of the mixture 4 formed by thermal transfer in this way is very difficult to peel off from the fabric 2. (6) is a schematic cross-sectional view of the obtained conductor 10A. In the conductor 10A, since the conductive surface composed of the layer of the mixture 4 is exposed, the conductive surface can be brought into contact with the skin of the person wearing the T-shirt 2.

  As an embodiment different from the conductor 10A, a conductor 10B can be exemplified. This will be described with reference to FIG. (1) and (2) in FIG. 3 are the same as (1) and (2) in FIG. (3) of FIG. 3 shows a state in which the layer of the mixture 4 is covered with the thermoplastic resin layer 6 when performing thermal transfer by applying an iron. (4) is a schematic cross-sectional view of the obtained conductor 10B. In the conductor 10 </ b> B, the conductive surface composed of the layer of the mixture 4 is covered with the thermoplastic resin layer 6. By adopting this embodiment, it is possible to insulate a region where the conductive surface does not need to be in contact with the skin of the person wearing the T-shirt 2.

  The bioelectrode of the third embodiment can be used not only for receiving a signal from a living body but also for applying an electrical stimulus (transmitting a signal) to the living body.

<< Pressure-sensitive sensor; Fourth embodiment >>
As shown in FIG. 4, the pressure-sensitive sensor according to the fourth embodiment of the present invention is arranged side by side so as to contact the cloth body 1 constituted by the conductor of the present invention and the conductive surfaces on both sides of the cloth body 1. And a plurality of conductive linear or belt-like members 7. Furthermore, the plurality of members 7 arranged substantially in parallel on the front surface (front surface) of the cloth body 1 are substantially the same as the plurality of members 7 arranged in parallel on the back surface of the cloth body 1. It arrange | positions so that it may orthogonally cross.

The size of the conductive surface of the cloth body 1 is not particularly limited, and is appropriately adjusted according to the application. In the cloth body 1 constituting the pressure-sensitive sensor 20 shown in FIG. 4, the entire surface (front surface) and back surface are conductive surfaces. The front surface and the back surface are electrically connected. As such a cloth body 1, a conductive cloth in which the fibrous conductor of the first embodiment (the conductive fiber in which the mixture is coated on the fiber) is used as the warp and / or the weft can be exemplified. Further, the cloth-like conductor of the first embodiment (the conductive cloth in which the mixture is coated on the cloth) can also be used as the cloth body 1. Since the conductive polymer is uniformly distributed in the conductive cloth, the conductive surface of the conductive cloth has substantially uniform conductivity. In addition, it retains breathability, flexibility and hygroscopicity as a fabric.
The cloth body 1 can also be used as a conductive surface constituting the biological electrode of the third embodiment.

The fabric constituting the fabric 1 is preferably a three-dimensional and thick knitted structure (woven fabric) or a woven or non-woven fabric having an overlapping structure. For example, a fabric having a spring-like structure (structure having elasticity) formed of fibers in the thickness direction, such as a 2-way tricot, a 1-way tricot, and a stocking, can be given. When pressure is applied to the conductive cloth 1 (conductive cloth) using such a cloth, the conductive polymer that is uniformly fixed to the cloth is compressed, stretched, bent, and the conductivity changes. (descend.
Furthermore, when pressure is applied to the conductive cloth 1 with a relatively soft object such as a finger, the contact area between the object surface deforming and the cloth body 1 increases as the pressure increases. Capacity (capacitance) increases. As an example of the capacitance change, there is an example in which the capacitance which was 9 picofarad (pF) at the time of non-contact increases to 20 pF at a light compression of 100 g and increases to 33 pF at a strong compression of 1000 g. The pressure-sensitive sensor 20 uses a change in at least one of these conductivity and capacitance.

  The linear or belt-like member 7 disposed on both surfaces of the cloth body 1 is not particularly limited as long as the surface thereof has conductivity. For example, the fibrous conductor of the first embodiment, PEDOT Thin fibers such as fibers, metal wires, metal ribbons, silver-coated nylon yarns coated with -PSS alone are preferable. Furthermore, a thin strip-like member such as a strip-like thin plate coated with a conductive material such as ITO, PEDOT-PSS or the mixture is preferable. The shape of the member 7 is linear or strip-shaped. The “strip shape” includes a rectangular shape or a strip shape. The cross-sectional shape of the member 7 is not particularly limited, and may be any shape such as a circle, a rectangle, and a polygon. The specific width and thickness of the member 7 are appropriately adjusted according to the application. For example, a linear or strip-shaped member having a width of 0.01 cm to 1 cm and a thickness of 0.01 cm to 0.5 cm can be given. By using such a linear or belt-like member 7, a grid in which a plurality of members 7 are arranged can be easily formed.

  The number of members 7 respectively disposed on the front and back surfaces of the pressure-sensitive sensor 20 is not particularly limited, and is appropriately set depending on the application. For example, in an application for detecting a pressing pressure (pressing) by a finger or palm, a configuration in which the members 7 are arranged on the front surface and the back surface at intervals of 0.1 cm to 1 cm, respectively. The number and interval of the members 7 arranged on the front surface and the number and interval of the members 7 arranged on the back surface may be the same or different. Further, the plurality of members 7 arranged on the front surface and the back surface may all be members of a unified shape or type, or members of a shape or type in which some of the plurality of members 7 arranged on the front surface and the back surface are different. It may be. Usually, in order to stabilize the pressure-sensitive characteristics of the pressure-sensitive sensor 20, it is preferable that all the members 7 are made of the same type of material and have a unified shape.

  On both surfaces of the cloth body 1 of the pressure sensor 20, silver coated nylon yarns are arranged in parallel at equal intervals of 4 mm. At this time, the group of silver-coated nylon yarns arranged on the front surface and the group of silver-coated nylon yarns arranged on the back surface are arranged so as to be substantially orthogonal to each other with the back surface seen through. . By arranging in this way, a grid having high-density intersections can be formed as shown in FIG. In FIG. 4A, an insulating cloth 9 described later is omitted. FIG. 4B is a schematic cross-sectional view of the pressure-sensitive sensor 20. Since the silver-coated nylon thread is bonded and fixed at an equal interval of 4 mm to the polyester insulating cloth 9 arranged on the outermost surfaces of both sides of the pressure-sensitive sensor 20, the position of each silver-coated nylon thread 7 is maintained. The In a state where no pressure is applied to the pressure sensor 20 (standby state), the silver-coated nylon thread 7 may be separated upward or downward without contacting (contacting) the conductive surface of the cloth body 1. In order to exhibit a more stable detection function, the silver-coated nylon yarn 7 is preferably in contact with the conductive surface of the cloth body 1 even in the standby state.

  The structure which combined the electrically conductive cloth which is the cloth body 1 illustrated here and the silver coat nylon thread which is the member 7, or the fibrous form of the first embodiment which is the electrically conductive cloth which is the cloth body 1 and the member 7. The pressure-sensitive sensor 20 having a structure combined with a conductor has high wearability required for a wearable device that is used in contact with the skin for a long period of time, that is, a touch feeling, thinness as a clothing material, It has sufficient flexibility and comfort at the time of wearing, in which the strength is complicated.

  FIG. 4C shows a state where pressure is applied so that the upper surface of the pressure-sensitive sensor 20 placed on the table 12 is pushed with the finger 11. FIG. 4D shows a state where pressure is applied so that the upper surface and the lower surface of the pressure sensor 20 are sandwiched between the fingers 11. When the finger 11 applies pressure to the pressure-sensitive sensor 20, the cloth body 1 is compressed, and the distance between the front surface member 7 and the back surface member 7 is shortened, so that the front surface member 7 is changed to the back surface member 7. The resistance value when the current flows to is reduced. A two-dimensional distribution of pressure applied to the pressure sensor 20 can be measured based on a change in resistance value (impedance) at the intersection of the members 7 constituting the grid.

  Since the pressure-sensitive sensor 20 shown in FIG. 4 includes the insulating cloth 9 made of an insulating material such as polyester on the outermost surface, the finger 11 does not touch the member 7 directly. Instead of this configuration, a pressure-sensitive sensor having a configuration excluding the insulating cloth 9 is cited as another embodiment A. In this embodiment A, the member 7 is fixed to the cloth body 1 by a conventional method such as bonding with an adhesive. Since the member 7 is exposed to the outside in the pressure-sensitive sensor of Embodiment A, the finger 11 directly touches the member 7. It is also possible to use the pressure sensitive sensor of Embodiment A as a touch sensor (contact sensor) by utilizing the fact that the electrical characteristics (capacity) of the member 7 change due to this contact. At this time, not only the member 7 senses the contact of the finger 11 but also it is possible to give an electrical stimulus (input a signal) from the member 7 to the finger 11. That is, by using the member 7 as an electrode for signal input to the living body and inputting a stimulus signal to the skin that is in contact with the member 7 constituting the pressure-sensitive sensor, feedback that the sensor is touched to the skin (sensation) is fed back. can do. In addition, muscle contraction, nerve stimulation, generation of evoked potential, and the like can be performed by appropriately adjusting the type and intensity of the stimulation signal and the part of the living body that the sensor contacts.

  In the pressure-sensitive sensor of Embodiment A, since the conductive surface of the cloth body 1 and the member 7 are exposed to the outside, the pressure-sensitive sensor is attached to the surface of a living body such as skin by attaching the pressure-sensitive sensor. It is also possible to function as a biological electrode.

  The pressure-sensitive sensor according to the fourth embodiment described above absorbs pressure in a predetermined region of the conductive cloth on which the grid is arranged, and changes the electrical characteristics of the conductive cloth due to deformation on both sides of the conductive cloth. Measurement is performed by deriving from the arranged member 7 (thread-like or belt-like electrode). For this reason, compared with a conventional pressure-sensitive sensor using only a filamentous electrode, the baseline is stable, the S / N ratio is high, and highly reliable pressure-sensitive characteristics can be obtained. Moreover, since the pressure-sensitive sensor of the fourth embodiment is thin and flexible, it is excellent in wearability. Furthermore, when the conductive surface of the cloth body 1 constituting the pressure-sensitive sensor has appropriate hydrophilicity, the conductivity when installed directly on the skin is further improved. Moreover, when it installs directly on skin, in addition to the function as a pressure-sensitive sensor, it can also have the function to acquire a biological signal as a biological electrode. Moreover, since the pressure-sensitive sensor of the fourth embodiment operates with a simple circuit, its pressure-sensitive characteristics can be easily adjusted.

<< Method for Producing Conductor; Fifth Embodiment >>
The method for producing a conductor according to the fifth embodiment of the present invention includes a resin composition containing a conductive polymer and at least one of a binder resin or a polymerizable compound (monomer) constituting the binder resin. It is a production method for coating the fiber or fabric by adhering to the fiber or fabric and solidifying or polymerizing the resin composition.

  The description of the conductive polymer, the binder resin, the polymerizable compound (monomer) constituting the binder resin, the fiber, and the fabric is the same as described above. For this reason, it will not be described repeatedly here.

  The resin composition may contain a solvent in order to dissolve the conductive polymer, the binder resin, and the monomer, or to adjust the viscosity. The type of the solvent is not particularly limited, and is appropriately selected according to the type and purpose of the resin. The mixing ratio of the solvent and the resin is not particularly limited, and is appropriately adjusted so that the resin composition can be attached to the fiber or the fabric. In addition to the solvent, the resin composition contains an auxiliary agent such as a polymerization initiator, a polymerization accelerator, a cross-linking agent that cross-links resins, a stabilizer, an antioxidant, a pigment, and a filler depending on the purpose. May be.

  The content of the conductive polymer in the resin composition is not particularly limited as long as the mixture obtained by solidifying the resin composition maintains the conductivity. For example, the content is 0.01 to 10% by weight. Preferably, 0.05 to 5% by weight is more preferable, and 0.1 to 3% by weight is still more preferable.

  The content of the binder resin in the resin composition is not particularly limited as long as the mixture obtained by solidifying the resin composition maintains electrical conductivity, but is preferably, for example, 0.05 to 50% by weight, 0.1-25 weight% is more preferable, and 3-8 weight% is still more preferable.

  The total content of the conductive polymer and the binder resin in the resin composition is not particularly limited as long as the mixture obtained by solidifying the resin composition maintains the conductivity. For example, 0.06 -60 wt% is preferable, 0.15-30 wt% is more preferable, and 4-8 wt% is still more preferable.

  The weight ratio of the conductive polymer and the binder resin in the resin composition is not particularly limited as long as the mixture obtained by solidifying the resin composition maintains the conductivity. For example, binder resin / conductivity High polymer = 1-100 is preferable, 2-10 is more preferable, and 4-6 is still more preferable.

  When the content of the conductive polymer and the binder resin in the resin composition is set to the above preferable range, and the balance is a solvent, the viscosity of the resin composition becomes appropriate and adheres to the fiber or fabric. This improves the workability and allows uniform adhesion.

  The method for attaching the resin composition to the fiber or fabric is not particularly limited, and known methods such as coating, printing, dipping, spraying, and dropping can be applied. After the resin composition is attached to the fiber or fabric, the resin composition is solidified (cured) or polymerized to change the resin composition to the mixture described in the first embodiment, and the mixture Is obtained by coating the fiber or fabric.

  The method of solidifying (curing) the resin composition is not particularly limited as long as the mixture is fixed to the fibers or fabric. For example, a method of vaporizing a solvent contained in the resin composition and drying the resin composition, a method of polymerizing the monomer contained in the resin composition, and forming a binder resin in the resin composition, Examples include a method in which binder resins and / or conductive resins contained in the resin composition are crosslinked with a crosslinking agent to form a three-dimensional network structure in the resin composition.

  Here, “solidify” means that the resin composition becomes the mixture, and the mixture changes to a state where the fiber or fabric can be coated. Therefore, the solidified resin composition (the obtained mixture) may or may not have a solid feeling (rigidity) like a plastic molded product. The solidified resin composition may have elasticity such as rubber, or may have flexibility such as gel.

Examples of the method for drying the resin composition include a method of blowing warm air and a method of heating.
As a method for polymerizing the monomer contained in the resin composition, for example, it may be cured by heating, or may be cured by irradiating light such as UV or visible light. In this case, it is preferable to add a conventionally known curing initiator or curing accelerator to the resin composition. Moreover, when the fiber or fabric to which the resin composition is adhered is thick, the thermosetting is preferable to the photocuring because the polymerization efficiency is increased.
The method for crosslinking the resins contained in the resin composition is not particularly limited, and can be performed by a conventional method.

  By adjusting the content of the conductive polymer contained in the resin composition, the conductivity of the obtained conductor can be adjusted. Usually, the higher the content of the conductive polymer, the higher the conductivity of the conductor.

  By selecting the type and content of the binder resin contained in the resin composition in accordance with the purpose, the properties of the obtained conductor can be adjusted. For example, hydrophilicity (hydrophobicity), wettability, water absorption, water resistance, abrasion resistance, peel resistance, chemical resistance, heat resistance, and the like can be adjusted. Usually, the higher the binder resin content, the more the properties of the binder resin can be reflected in the conductor.

The manufacturing method of the fifth embodiment does not require a special and expensive apparatus, and can mass-produce conductors at low cost and high efficiency.
When the base material constituting the conductor is a fiber, the fiber can be processed into a desired form, and thus a conductor having a desired shape can be manufactured. By incorporating a fibrous or cloth-like conductor into a conventional garment, a wiring made of the conductor can be installed in the garment or a conductive surface made of the conductor can be installed.
When the base material which comprises the said conductor is a cloth, the conductor which has a desired-shaped conductive surface can be manufactured by printing the said resin composition in the desired area | region of the said cloth. If the shape of the conductive surface is an elongated rectangle or a line, the conductive surface can also function as an electrical wiring. Furthermore, it is possible to form a complicated electric circuit or an electric binding part (connector part) on the cloth by the printing or the like.

  EXAMPLES Next, although an Example is shown and this invention is demonstrated further in detail, this invention is not limited to a following example.

[Example 1; Production of conductive cloth]
A mixed solution (resin composition) containing 52, 42, 5, 1 (% by weight) of ethanol, water, polymethacrylic acid, and PEDOT-PSS was prepared. After immersing the blended fabric (5 cm × 10 cm) in the mixed solution for 5 minutes, the blended fabric was dried by applying warm air using a dryer to obtain a conductive fabric in which the mixed solution was solidified. When a probe of a resistance measuring device was applied to the surface of the conductive cloth and measured with a direct current of 5 V, the electric resistance value of the conductive cloth was 200 kΩ / cm.

Details of each material used in Example 1 are as follows.
As the blended fabric, “SILKY DRY” (registered trademark) (first reading, manufactured by Toray Industries, Inc.) made of polyester (containing 87%) and polyurethane (containing 13%) was used. Ethanol manufactured by Kanto Chemical Co. was used. As the water, purified water produced by MILLI-Q (registered trademark) (manufactured by Merck) was used. Polymethacrylic acid manufactured by Scientific Polymer Products Inc. was used. For PEDOT-PSS, Clevious P (manufactured by Heraeus, Germany) was used.

[Example 2; Production of conductive cloth]
The same procedure as in Example 1 was performed except that 5% by weight of polymethylmethacrylic acid (Aldrich Chemical) was used instead of polymethacrylic acid. The electric resistance value of the obtained conductive cloth was 1 MΩ / cm.

[Example 3; Production of conductive cloth]
It carried out similarly to Example 1 except having used 5 weight% of polyacrylic acid (made by Scientific Polymer Products Inc.) instead of polymethacrylic acid. The electric resistance value of the obtained conductive cloth was 100 kΩ / cm.

[Reference Example 1: Production of conductive cloth]
A mixed solution was prepared in the same manner as in Example 1 except that 5% by weight of polyvinyl alcohol (Wako Pure Chemical Industries) was used instead of polyacrylic acid. After immersing the blended fabric in this mixed solution for 5 minutes, the blended fabric was dried with a dryer and further immersed in ethanol for 5 minutes to chemically fix the mixture composed of PEDOT-PSS and polyvinyl alcohol. . Thereafter, a conductive cloth was prepared by drying with a dryer.
When measured in the same manner as in Example 1, the electric resistance value of the obtained conductive cloth was 1.2 MΩ / cm.

[Comparative Example 1; Production of conductive cloth]
The blended fabric was immersed in a solution obtained by adding 0.1% of EDOT (manufactured by Heraeus, Germany) to PEDOT-PSS. Subsequently, the mixed cloth was energized using a comb-shaped electrode, and PEDOT-PSS was electrochemically fixed on the surface and inside of the mixed cloth, thereby obtaining a conductive cloth of Comparative Example 1. Furthermore, the fixed PEDOT-PSS was impregnated with glycerol to give a treatment for improving water resistance.

  Since the fabric of Comparative Example 1 shown here is small, it can be manufactured relatively easily. However, the production by the electrochemical method of Comparative Example 1 requires a uniform current density and a relatively long processing time in order to fix PEDOT-PSS to the fabric. When manufacturing continuously on a mass production scale, apply a uniform current density to a device that can apply a uniform current density to a large fabric or a yarn that is a material constituting the fabric. It is necessary to have a device that can However, such a device is special and requires high capital investment.

<Evaluation of water resistance>
The conductive cloth produced in Examples 1 to 3 and Comparative Example 1 was immersed in purified water, and the rate at which PEDOT-PSS was eluted was examined. For the conductive fabrics of Examples 1 to 3, no obvious change was observed even after 2 months from immersion, and no dissolution of PEDOT-PSS was confirmed. On the other hand, with regard to the conductive cloth of Comparative Example 1, no obvious change was observed after 2 weeks from the immersion, but discoloration of the cloth and water coloring occurred after one month. From this state, it was confirmed that PEDOT-PSS eluted into water. Furthermore, it was confirmed that the conductive cloth was completely discolored and lost its conductivity two months after the immersion.
From the above results, the conductive cloths (conductors) of Examples 1 to 3 having PEDOT-PSS kneaded into the acrylic resin as the binder resin are more than the electrochemically fixed conductive cloth of the comparative example. It is clear that the water resistance is excellent.

Example 4 Production of Bioelectrode and Biosignal Measuring Device
The liquid mixture prepared in Example 1 was applied to a thermal transfer sheet (T-shirt transfer paper; manufactured by Canon Inc.) cut out in accordance with the size (2.5 cm × 4 cm) of the electrode surface, and heated with hot air from a dryer for 5 minutes. Dried. The dried electrode surface (conductive surface) was reversed to the back side, attached to the base of the thermal transfer sheet, and temporarily fixed. Thereafter, the thermal transfer sheet was placed on the position of the front chest on the inside of the T-shirt, and a bio-electrode was produced by thermal transfer using a household iron so that the electrode surface was finally exposed (FIG. 2). Furthermore, another bioelectrode having a similar electrode surface was placed on the upper arm of the T-shirt.
Next, silver-coated nylon thread is sewn on each electrode surface, and this silver-coated nylon extension is connected to the EC800 RS800CX (manufactured by Polar) installed on the shoulder of the T-shirt. did. Further, an intermediate portion of the wiring was sandwiched between a separately prepared thermal transfer sheet and a T-shirt, and an insulation coating was made (FIG. 1).

  An adult male wore the produced T-shirt type biological signal measuring device, and the heart rate was measured continuously for 18 hours. The results of the change over time are shown in FIG. In FIG. 1C, the horizontal axis indicates time, and the vertical axis indicates the heart rate per minute. From this result, it is clear that the biological signal measuring apparatus of the present invention can record biological signals stably for a long time from daytime activities to nighttime sleeping.

[Example 5: Production of pressure sensor and pressure sensor device]
Using a lycra (registered trademark) (manufactured by Toray Operontex Co., Ltd.), which is a stretchable cloth, a conductive cloth having a size of 4 cm × 4 cm and a thickness of 600 μm imparted with conductivity in the same manner as in Example Produced.
Next, prepare two pieces of insulating fabric with plain weave of polyester yarn, and place 10 silver coated nylon threads (2ply; made by Spark Fun) in parallel at intervals of 4 mm on one side of each insulating fabric. did. Each insulating cloth was placed on the front and back surfaces of the previously produced conductive cloth so that each silver-coated nylon thread was in contact with the surface of the conductive cloth, thereby producing a pressure-sensitive sensor. At this time, the silver-coated nylon yarn arranged on the front surface (front surface) and the silver-coated yarn arranged on the back surface were arranged so as to be orthogonal to each other (FIG. 4).

  A pressure-sensitive sensor device was obtained by selecting one silver-coated nylon thread of the produced pressure-sensitive sensor from the front and back surfaces and connecting it to a digital multimeter (NF circuit design block DM2561). FIG. 5 shows the relationship between the pressure and the resistance value when the selected two yarns pressurize at a position perpendicular to each other with the conductive cloth interposed therebetween. The horizontal axis of FIG. 5 shows the applied pressure (g: grams), and the vertical axis shows the resistance value (kΩ). As is clear from the results of FIG. 5, the pressure-sensitive sensor device of this example can detect a pressure change of 20 to 1000 grams with high sensitivity and high accuracy.

  The configurations and combinations thereof in the embodiments described above are examples, and the addition, omission, replacement, and other modifications of the configurations can be made without departing from the spirit of the present invention. Further, the present invention is not limited by each embodiment, and is limited only by the scope of the claims.

  The electric conductor, the electric conductor manufacturing method, the pressure sensitive sensor, the biological electrode, the pressure sensitive sensor device, and the biological signal measuring device according to the present invention are widely used in a wide range of fields such as medical treatment, health promotion, information technology, and wearable computers. Is possible.

DESCRIPTION OF SYMBOLS 1 ... Conductor (cloth body), 2 ... Cloth (T-shirt), 3 ... Electrocardiograph, 4 ... Mixture, 5 ... Conductive thread (silver coat nylon thread), 6 ... Thermal transfer sheet, 7 ... Member (silver) Coated nylon thread), 8 ... mount, 9 ... insulating cloth, 10 ... bioelectrode, 10A, 10B ... conductor, 11 ... finger, 12 ... stand, 20 ... pressure sensor

Claims (2)

A fabric comprising a conductive polymer coated with a conductive polymer having a hydrophilic property and a binder resin coated on a fiber or fabric;
The side by side so as to contact both sides of the conductive surface of the fabric body is arranged, comprising a plurality of conductive linear member made of a fiber coated with a conductive polymer having a hydrophilic and,
A plurality of the members arranged in parallel on the surface of the conductive surface,
A pressure-sensitive sensor, which is arranged so as to be substantially orthogonal to the plurality of members arranged in parallel on the back surface of the conductive surface. A pressure-sensitive sensor device comprising: the pressure-sensitive sensor according to claim 1; and an external device connected to the pressure-sensitive sensor and transmitting / receiving a signal to / from the pressure-sensitive sensor.

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