JP2019068901A - Bioelectrode and garment having the same - Google Patents

Abstract

To provide a bioelectrode capable of acquiring a bioelectric signal with a high degree of precision even when a sensor attaching part or clothing becomes wet with sweat or the like.SOLUTION: A bioelectrode 10 includes: a sensor attaching part 1; a first electrode part 21 and a second electrode part 22 arranged on a side of the surface of the sensor attaching part that comes in contact with a living body; a first connector 31 and a second connector 32 for electrically connecting a bioelectric signal measuring device arranged on a side of the surface of the sensor attaching part that does not come in contact with the living body to the first electrode part and the second electrode part; and first wiring 41 and second wiring 42 for electrically connecting the first electrode part and the second electrode part to the first connector and the second connector. The sensor attaching part includes a separation part S in which a section where the first electrode part, the first connector, and the first wiring are disposed is separated from a section where the second electrode part, the second connector, and the second wiring are disposed, and through the separation part, the first connector and the second connector are connected to the bioelectric signal measuring device.SELECTED DRAWING: Figure 1

Description

  The present invention relates to a bioelectrode and a garment comprising the same.

  Conventionally, biological electrodes used for obtaining and recording bioelectric signals such as electrocardiograms, electromyograms, electroencephalograms, and heart rate fluctuations, and for applying electrical stimulation to a living body are known. The bioelectrode is used in intimate contact with the body surface.

  Although bioelectric signals have been acquired in a state where the living body is at rest, in recent years, attempts have been made to continuously acquire bioelectric signals for a long time in daily life and use them for health management and the like. For example, a so-called wearable electrode in which a living body electrode is fixed to clothes or the like is transmitted in real time to an electronic device such as a smartphone or a tablet terminal by transmitting a living body electrical signal acquired by the living body electrode to electronic devices such as a smartphone or a tablet terminal. Attempts are being made to utilize it in the field.

JP, 2016-106877, A

  As described in Patent Document 1, in general, as the body cloth of clothes, a material that absorbs moisture such as sweat or rain is used to ensure comfort when worn, and a body containing an electrolyte solution is used. The fabric loses its electrical insulation. For this reason, the conventional biological electrode can not ensure electrical insulation between the conductor, such as the electrode, the connector, and the wiring and the body, when the wearer sweats or when it is used in rainy weather, and it is other than the electrode The bioelectric signal detected in the body part of the body is mixed with the bioelectric signal acquired from the electrode unit, so that a desired bioelectric signal can not be acquired, or a plurality of electrodes are electrically shorted. There is a problem that the signal is degraded.

  As a living body electrode which solves such a conventional subject, in patent documents 1, the sensor attachment part which consists of a water-repellent and electric insulating member, and the electric conduction arranged on the side which contacts the living body of this sensor attachment part A connector for connection to a bioelectric signal measuring device provided so as to be exposed on the side of the sensor mounting unit not in contact with a living body, and an electrode unit made of a flexible member, and fixed to the sensor mounting unit A wiring electrically connecting the electrode portion and the connector; and a water-repellent and electrically insulating insulating member covering a portion of the surface of the connector and the wiring in contact with a living body. A bioelectrode is disclosed.

  In the biological electrode described in Patent Document 1, after the biological electrode is attached to the clothing by covering the surface of the connector and the wiring in contact with the living body, the clothing is wet with sweat etc. Even if it becomes, a desired bioelectric signal can be obtained.

  However, when the present inventors repeatedly studied, in the case of the conventional biomedical electrode as disclosed in Patent Document 1, although the bioelectric signal can be obtained when the clothing becomes wet with sweat etc., its accuracy It was found that it may be insufficient. The inventors further studied the reason, and as a result, a slight short circuit occurs between the electrode parts arranged at two places through the wet clothes and the sensor attachment part, and thus, they are obtained. It is clear that the accuracy of the bioelectric signal is decreasing. For example, when the detection target of the living body electrode is an electrocardiogram waveform, generally, the electrode portions are arranged at two places near the heart of the living body and near the heart away from the heart, but the electrode parts arranged at two places It has been found that when a short circuit occurs between the two, there is a problem that the accuracy of the obtained bioelectric signal is reduced.

  SUMMARY OF THE INVENTION In view of the above-described problems of the prior art, the present invention provides a bioelectrode capable of acquiring a bioelectric signal with high accuracy even when the sensor attachment portion or clothes (clothing) get wet with sweat or the like. The main purpose is to

  The present inventors have intensively studied in view of the above problems. As a result, the sensor attachment portion, the first electrode portion and the second electrode portion disposed on the side of the sensor attachment portion in contact with the living body, and the living body disposed on the surface side of the sensor attachment portion not in contact with the living body A first connector for electrically connecting an electrical signal measuring device to the first electrode portion, and a second connector for electrically connecting the bioelectric signal measuring device to the second electrode portion; The sensor includes a first wire electrically connecting the first electrode portion and the first connector, and a second wire electrically connecting the second electrode portion and the second connector, and the sensor The attachment portion is a portion where the first electrode portion, the first connector, and the first wire are disposed, and a portion where the second electrode portion, the second connector, and the second wire are disposed. Have a separation part between them and And the bioelectrical signal measuring device is joined with the first connector and the second connector via the separation part, and the separation part is a bioelectrode engaged by the insulating engagement member. Also, it has been found that bioelectric signals can be obtained with high accuracy even when the sensor attachment portion and clothes (clothing) become wet due to sweat or the like. The present invention has been completed by conducting further studies based on these findings.

That is, the present invention provides the inventions of the aspects listed below.
Item 1. Sensor mounting area,
A first electrode unit and a second electrode unit disposed on the side of the sensor attachment unit in contact with the living body;
The first connector for electrically connecting a bioelectric signal measuring device disposed on the side of the sensor attachment portion not in contact with the living body with the first electrode portion, and the bioelectric signal measuring device, A second connector for electrically connecting to the two electrodes;
A first wire electrically connecting the first electrode portion and the first connector; and a second wire electrically connecting the second electrode portion and the second connector;
Equipped with
The sensor attachment portion includes a portion where the first electrode portion, the first connector, and the first wiring are disposed, and the second electrode portion, the second connector, and the second wiring. And a separation part separated from the
The first connector, the second connector, and the bioelectric signal measurement device are joined via the separation unit,
The separation unit is engaged by an insulating engagement member.
Item 2. The biological electrode according to Item 1, wherein a first water permeation suppression layer and a second water permeation suppression layer are provided along the outer peripheral portions of the first electrode portion and the second electrode portion, respectively.
Item 3. Item 3. The bioelectrode according to Item 2, wherein the first moisture permeation suppressing layer and the second moisture permeation suppressing layer are each formed of an elastic member.
Item 4. The bioelectrode according to any one of Items 1 to 3, wherein each of the first electrode portion and the second electrode portion is made of a fiber fabric.
Item 5. In any one of Items 1 to 4, wherein the first electrode unit and the second electrode unit are provided on the first base material layer and the second base material layer disposed in the sensor attachment unit, respectively. Bioelectrode as described.
Item 6. Item 6. The bioelectrode according to any one of Items 1 to 5, which is in the shape of a belt.
Item 7. Item 5. A garment, wherein the biological electrode according to any one of Items 1 to 5 is fixed such that the first electrode unit and the second electrode unit are in contact with a living body.

  According to the present invention, it is possible to provide a bioelectrode capable of acquiring a bioelectric signal with high accuracy even when the sensor attachment portion or the clothing becomes wet due to sweat or the like. Furthermore, according to the present invention, it is possible to provide a garment in which the bioelectrode is fixed.

It is a schematic-drawing sectional drawing of an example of the bioelectrode of this invention. It is schematic-drawing sectional drawing which shows an example of the positional relationship of the electrode part of the biological electrode of this invention, and a water permeation suppression layer. It is schematic-drawing sectional drawing which shows an example of the positional relationship of the electrode part of the biological electrode of this invention, and a water permeation suppression layer. It is a schematic-drawing sectional drawing which shows an example of the positional relationship of the electrode part of the biological electrode of this invention, a water permeation suppression layer, and a base material layer. It is a schematic diagram of an example in case the bioelectrode of this invention has belt shape. It is a schematic diagram of an example of the clothes to which the bioelectrode of this invention was fixed. It is a schematic diagram of an example of the clothes to which the bioelectrode of this invention was fixed. It is a schematic diagram of an example of the clothes to which the bioelectrode of this invention was fixed. FIG. 6 is a schematic view of a belt-shaped biological electrode of Comparative Example 1; 7 is a heartbeat waveform of Example 1; 7 is a heartbeat waveform of Comparative Example 1; 7 is a heartbeat waveform of Comparative Example 2;

[Bioelectrode]
The biological electrode according to the present invention includes a sensor attachment portion, a first electrode portion and a second electrode portion disposed on the side of the sensor attachment portion in contact with the living body, and a surface side of the sensor attachment portion not in contact with the living body. A first connector for electrically connecting the disposed bioelectric signal measuring device to the first electrode unit, and a second connector for electrically connecting the bioelectric signal measuring device to the second electrode unit And 2) a connector, a first wire electrically connecting the first electrode portion and the first connector, and a second wire electrically connecting the second electrode portion and the second connector. The sensor attachment portion includes a portion where the first electrode portion, the first connector, and the first wiring are disposed, and the second electrode portion, the second connector, and the second wiring. Between the part being A separation part is provided, and the first connector and the second connector are joined to the bioelectric signal measurement device via the separation part, and the separation part is engaged by the insulating engagement member It is characterized by being According to the bioelectrode of the present invention having such a configuration, bioelectric signals can be obtained with high accuracy even when the sensor attachment portion or the clothing becomes wet due to sweat or the like. Hereinafter, the bioelectrode of the present invention and a garment provided with the same will be described in detail with reference to FIGS. 1 to 8.

  As shown in FIG. 1, the biological electrode 10 includes at least a sensor attachment portion 1, a first electrode portion 21, a second electrode portion 22, a first connector 31, a second connector 32, and a first wiring. 41 and a second wiring 42 are provided.

<Sensor mounting part>
In the living body electrode of the present invention, the electrode portion is disposed on the side of the sensor attachment portion in contact with the living body. FIG. 1 shows that the first electrode unit 21 and the second electrode unit 22 are respectively disposed on the side of the surface X of the sensor attachment unit 1 in contact with the living body.

  Moreover, the connector is arrange | positioned at the surface side which does not contact the biological body of a sensor attachment part. FIG. 1 shows that the first connector 31 and the second connector 32 are arranged on the side Y of the sensor attachment unit 1 not in contact with the living body. The first connector 31 is provided to electrically connect the bioelectric signal measuring device to the first electrode unit 21. The second connector 32 is provided to electrically connect the bioelectric signal measuring device to the second electrode unit 22. When the bioelectrode 10 acquires a bioelectric signal, the first connector 31 and the second connector 32 and the bioelectric signal measuring device are joined. Furthermore, the first wiring 41 electrically connects the first electrode portion 21 and the first connector 31. Further, the second wiring 42 electrically connects the second electrode portion 22 and the second connector 32.

  The sensor attachment portion is a member that arranges at least the electrode portion, the connector 31, and the wiring 41 so that the biological electrode can be fixed to a living body, clothes, or the like.

  The material constituting the sensor attachment portion is not particularly limited. For example, natural fiber materials such as cotton and wool, regenerated fiber materials such as rayon and cupra, and electrically insulating synthetic resin such as polyester, nylon, acryl and urethane There is a material. The material constituting the sensor attachment portion may be one type or two or more types.

  As shown in FIG. 1, the sensor attachment portion 1 includes a portion where the first electrode portion 21, the first connector 31, and the first wiring 41 are disposed, a second electrode portion 22, a second connector 32, and It has a separation portion S (a portion where the sensor attachment portion 1 is not present) separated from the portion where the second wiring 42 is disposed, and the separation portion S is an insulating engagement member 50 are engaged.

  The separation distance d at the separation portion S (that is, the distance between the portions where the sensor attachment portion 1 is not present) is not particularly limited, but bioelectric signals while securing good attachment of the biological electrode 10 to the living body From the viewpoint of obtaining with high accuracy, for example, about 0.05 to 10 cm, preferably about 0.1 to 10 cm, more preferably about 0.2 to 5 cm, and still more preferably about 0.2 to 1 cm. If it is less than the lower limit value, water may be transmitted to short circuit between the electrodes, and if it exceeds the upper limit value, the comfort may be impaired.

  The shape of the sensor attachment portion is not particularly limited. For example, as shown in FIG. 5, when the bioelectrode 10 has a belt shape, the first electrode portion 21, the second electrode portion 22, and the first connector 31 may be provided on the belt-shaped sensor attachment portion 1. The second connector 32, the first wiring 41, and the second wiring 42 can be disposed to form the living body electrode 10. Further, as shown in FIGS. 6 to 8, in the case of fixing the bioelectrode 10 to the clothes 80, the shape (for example, a rectangular shape) suitable for fixing to the clothes 80 may be used. Further, even when the bioelectrode is formed into a belt shape, the sensor attachment portion may be formed into, for example, a rectangular shape and fixed to a belt-shaped member to form a belt-shaped bioelectrode. Here, the belt shape refers to being annular, and it is a concept including not only waist band-like ones, but also aspects such as, for example, belly wrap, arm cover (sleeve), etc. It does not exclude that components (for example, a strap etc.) other than the parts which form are attached, nor does its width and size be limited.

  When the bioelectrode 10 is in the shape of a belt, when the bioelectrode 10 is attached to the biomedical body, the separation portion S is engaged by the insulating engagement member 50 described later to measure the bioelectrode 10 such as the chest circumference It can be suitably attached to a place. Further, in the case of a garment in which the biological electrode is fixed, the biological electrode can be worn by wearing the garment 80 and engaging the separation portion S with an insulating engagement member 50 (for example, an insulating fastener or the like) described later. 10 can be suitably attached to measurement points, such as chest circumference.

  In addition, although illustration is abbreviate | omitted, in addition to the isolation | separation part S between the 1st electrode part 21 and the 2nd electrode part 22, when the biological electrode of this invention is belt shape as shown, for example in FIG. Also on the opposite side of the belt shape, the sensor mounting portion 1 may have a separated portion. When the living body electrode of the present invention has such two separated portions, the living body electrode 10 is provided with the first electrode portion 21, the first connector 31 and the first wiring 41 in the sensor attachment portion 1. It becomes possible to divide into two members of which the second electrode portion 22, the second connector 32 and the second wiring 42 are disposed in the sensor attachment portion 1.

<Electrode part>
In the biological electrode of the present invention, the electrode unit is disposed so as to be exposed on the side of the sensor attachment unit that contacts the living body.

  The material constituting the electrode portion (the first electrode portion 21 and the second electrode portion 22) is not particularly limited as long as it has conductivity, and, for example, a conductive fiber fabric, a conductive resin film And metal foils. Among them, conductive textiles, conductive resin films are preferable from the viewpoint of obtaining bioelectric signals with high accuracy even when the sensor attachment portion or the clothing becomes wet with sweat or the like. From the viewpoint of being excellent in the wearing feeling of the biological electrode, the conductive fiber knit is more preferably mentioned.

  From the viewpoint of imparting conductivity to the fiber knit fabric, the fiber knit fabric preferably contains conductive fibers. The conductive fiber is not particularly limited, and a known fiber having conductivity can be used. Specific examples of the conductive fiber include metal plated fiber, conductive polymer fiber, metal fiber, carbon fiber, slit fiber, conductive material-containing fiber and the like. The conductive fibers may be used alone or in combination of two or more.

  The metal-plated fiber is not particularly limited, and any known metal-plated fiber can be used. For example, the surface of the synthetic fiber is coated with a metal such as silver, copper, gold, stainless steel, or an alloy containing at least one of them. Fibers are included. As a synthetic fiber to which metal plating is given, Preferably a nylon fiber, polyester fiber, etc. are mentioned.

  The conductive polymer fiber is not particularly limited, and known ones can be used, for example, poly (3,4-ethylenedioxythiophene) (PEDOT) to polystyrene sulfonic acid (poly 4-styrene sulfonate; PSS) Examples thereof include PEDOT / PSS fibers using doped PEDOT / PSS, and fibers in which PEDOT / PSS and a matrix resin are complexed. As a matrix resin, polyvinyl alcohol (PVA) etc. are mentioned. Moreover, what impregnated the conductive polymer in the synthetic fiber may be used. Examples of synthetic fibers include polyester fibers and nylon fibers.

  The metal fiber is not particularly limited, and fibers made of a metal such as silver, nickel, copper, iron, tin or an alloy containing at least one of these metals can be mentioned.

  As the conductive material-containing fiber, a fiber made of a fiber-forming polymer such as a polyester-based polymer or a polyamide-based polymer uniformly dispersed with a conductive substance (that is, a conductive polymer) is useful. Examples of the conductive substance include conductive carbon blacks such as furnace black, ketjen black, acetylene black and channel black; single metals such as silver, nickel, copper, iron and tin; copper sulfide, zinc sulfide, copper iodide And other metal compounds.

  Among the conductive fibers, silver-plated nylon fibers, silver-plated polyester fibers, and fibers composited with PEDOT / PSS with a matrix resin such as PVA are preferable.

  The electrical resistance value of the conductive fiber is not particularly limited, but, for example, about 0.1 to 100,000 Ω / 10 cm can be mentioned.

  The fiber knitted fabric may be composed of only conductive fibers or may further contain other fibers. As other fibers, preferably heat-fused fibers or heat-bonded fibers (hereinafter referred to as heat-fused fibers etc.) can be mentioned. The difference between the heat-fusion fiber and the heat-cohesion fiber can be distinguished by the strength of the bond strength generated by cooling from the semi-molten or softened state, and the one with strong bond strength is the heat-fusion fiber, and The one with weak strength is heat-bonded fiber. Although this distinction does not say clearly and includes the part made into vague imitation paste, in short, it shall be a fiber which can combine the crossing part of fibers by heat treatment. For example, Mobilon R, Mobilon R-L manufactured by Nisshinbo Textile Co., Ltd. can be exemplified as a polyurethane fiber as a heat fusion fiber, and Asahi Kasei as a example of a polyurethane fiber which is both a heat fusion fiber and a heat cohesion fiber Loika SF etc. made in corporation can be illustrated. When the fiber knitted fabric further contains a heat fusible fiber or the like, the surface smoothness of the electrode portion is improved by subjecting the electrode portion including the conductive fiber and the heat fusible fiber or the like to heat pressing (that is, the surface The roughness (Ra) can be reduced to improve the adhesion to the skin (body surface). By enhancing the adhesion of the bioelectrode to the skin, bioelectric signals can be obtained with higher accuracy.

  The heat fusible fiber and the like are not particularly limited as long as the fibers are bonded to each other by, for example, heat pressing at about 80 ° C. or higher, and preferably polyurethane fiber, nylon fiber, polyester fiber, and the like. The heat-fusion fibers and the like may be used alone or in combination of two or more.

  When the fiber knitted fabric further includes a heat-fusion fiber or the like, the mass ratio of the conductive fiber to the heat-fusion fiber or the like in the fiber fabric (electroconductivity) from the viewpoint of acquiring bioelectric signals with higher accuracy. As the fibers: heat-fusion fibers etc., preferably about 50:50 to 98: 2, and more preferably about 60:40 to 90:10.

  It does not restrict | limit especially as a fineness of the electroconductive fiber which comprises fiber knitted fabric, For example, about 1-300 dtex is mentioned. The conductive fibers may be monofilaments or multifilaments. The fineness of the heat-fused fiber and the like is not particularly limited, and may be, for example, about 1 to 300 dtex. The heat fusible fiber or the like may be a monofilament or a multifilament. The knitting method of the fiber knitted fabric is not particularly limited, and, for example, other than weft knitting such as single knitting (also referred to as plain knitting or tengu knitting), milling (also referred to as rubber knitting), pearl knitting, smooth knitting, etc. And known knitting methods including warp knitting and braiding.

  The conductive resin film is not particularly limited, and examples thereof include those formed by printing a conductive ink. Preferred examples of the conductive resin film include printed films printed with conductive inks (including paste-like ones) such as silver ink, copper ink and carbon ink, and conductive filler dispersed films such as metal powder. Be

  Moreover, it does not restrict | limit especially as metal foil, For example, copper foil, aluminum foil, nickel foil etc. are mentioned.

  Furthermore, it is preferable that the surface of the fiber knitted fabric has either a hydrophobic surface or a hydrophilic surface from the viewpoint of acquiring bioelectric signals with higher accuracy.

  For example, if the hydrophobicity of the surface of the electrode portion is very high, it is possible to efficiently retain the water released from the skin between the skin and the surface of the electrode portion. As a result, the contact impedance between the skin and the electrode unit is reduced, and as a result, an artifact is less likely to be taken in the bioelectric signal, and the acquisition accuracy of the bioelectric signal is improved.

  Moreover, when the hydrophilicity of the electrode part is very high, it is possible to efficiently retain the water released from the skin to the electrode part. As a result, the moisture content of the electrode itself is improved, and as a result, an artifact is less likely to be taken in the bioelectric signal, and the acquisition accuracy of the bioelectric signal is improved.

  For example, a method for providing a hydrophobic treatment layer in an electrode part is not particularly limited, and for example, a method in which the electrode part is immersed in a hydrophobic surface treatment liquid can be mentioned. In addition, after immersion, drying or heat treatment may be performed, whereby the durability of the hydrophobically treated layer can be further improved.

  The hydrophobic surface treatment liquid is not particularly limited, and known hydrophobic surface treatment liquids can be used. Examples of the hydrophobic surface treatment liquid include fluorine-based hydrophobic surface treatment liquid, silicone-based surface treatment liquid, and wax-based surface treatment liquid. These hydrophobic surface treatment solutions are readily commercially available.

  Although it does not restrict | limit especially as a method to provide a hydrophilic treatment layer in the surface of an electrode part, For example, the method of immersing an electrode part in a hydrophilic surface treatment liquid is mentioned. In addition, after immersion, drying or heat treatment may be performed, whereby the durability of the hydrophilically treated layer can be further improved.

  It does not restrict | limit especially as a hydrophilic surface treatment liquid, A well-known hydrophilic surface treatment liquid can be used. As a hydrophilic surface treatment liquid, a polyurethane type hydrophilic surface treatment liquid, a polyether type surface treatment liquid, a polyester type surface treatment liquid etc. are mentioned, for example. These hydrophilic surface treatment solutions are readily commercially available.

  The thickness t of the electrode portion is not particularly limited, but is preferably 10 mm or less, more preferably about 0.01 to 5 mm, still more preferably 0.02 to 2 mm, from the viewpoint of acquiring bioelectric signals with higher accuracy. The degree is mentioned. More specifically, when the electrode portion is made of a fiber knit, the thickness t of the electrode portion is preferably about 0.05 to 5 mm, more preferably about 0.1 to 2 mm. When the electrode portion is formed of a conductive resin film, the thickness t of the electrode portion is preferably about 0.01 to 5 mm, more preferably about 0.02 to 2 mm. When the electrode portion is formed of a metal foil, the thickness t of the electrode portion is preferably about 0.005 to 5 mm, more preferably about 0.02 to 2 mm.

  The distance W (the shortest distance) between the first electrode unit 21 and the second electrode unit 22 is not particularly limited, and can be appropriately set according to the type of bioelectric signal to be acquired. For example, if the biological electrode 10 acquires an electrocardiogram waveform, it is preferably 1 cm or more, more preferably 2 cm or more, from the viewpoint of acquiring the bioelectric signal with higher accuracy. If it is less than this, the biosignal may not be correctly extracted. As shown in FIG. 1, in the biological electrode 10, a separation unit S in which the sensor attachment unit 1 does not exist is provided between the first electrode unit 21 and the second electrode unit 22, and The separation portion S is engaged by the insulating engagement member 50. Therefore, in the living body electrode 10, even when the distance W between the first electrode portion 21 and the second electrode portion 22 is small, a short circuit between the first electrode portion 21 and the second electrode portion 22 is effectively suppressed. The bioelectric signal can be acquired with high accuracy.

In addition, the area of the electrode portion on the surface side in contact with the living body is not particularly limited, and can be appropriately set according to the type of bioelectric signal to be acquired. For example, in the case of obtaining the electrocardiographic waveform, bioelectrical signal more from the viewpoint of obtaining more accurately, and preferably about ² 0.1～70Cm, more preferably include about 0.12～40Cm ² . If it is less than the lower limit value, it may be difficult to touch the skin due to the unevenness of the skin surface, and if it exceeds the upper limit value, it will be out of the hard movement area and it will be susceptible to the movement of the body. May increase.

  In the present specification, in order to simplify the description, the case where the biological electrode 10 has two electrode parts of the first electrode part 21 and the second electrode part 22 is exemplified. In addition to the 1st electrode part 21 and the 2nd electrode part 22, one or more other electrode parts may be provided in a living body electrode.

<Water permeation suppression layer>
As shown in FIG. 2 to FIG. 4, the biological electrode has a moisture permeation suppression layer (a first moisture permeation suppression layer 61 and a second moisture permeation suppression layer 62) on the side of the sensor attachment portion in contact with the organism. It is preferable that it is arrange | positioned. In the bioelectrode according to the present invention, the provision of the moisture permeation suppressing layer makes it possible to more efficiently retain the moisture released from the skin between the skin and the surface of the electrode portion, thereby achieving bioelectricity. Signals can be acquired with higher accuracy.

  In the biological electrode 10, the water permeation suppressing layer is not particularly limited as long as it can suppress the moisture permeation of the biological electrode, and can be made of a resin film, a non-woven fabric, or the like. As a material which comprises a water permeation suppression layer, polyurethane, a polyethylene terephthalate, an acrylic resin, polyethylene, a polypropylene, nylon etc. are mentioned. Further, the moisture permeation suppressing layer can be formed of a non-woven fabric. The water permeation suppressing layer may be a single layer or a multilayer. Moreover, when a water permeation | transmission suppression layer is a multilayer, the raw material which comprises each layer may be the same, and may differ.

The moisture permeability of the moisture permeation suppressing layer is not particularly limited, but preferably 200 g / m ² / h or less, more preferably 150 g / m ² / h or less. In addition, the moisture permeability of a moisture permeation suppression layer is the value measured by the method of JISL1099 (A-1 method).

  Further, in the biological electrode of the present invention, the water permeation suppressing layer is preferably provided along the outer peripheral portion of the electrode portion. Specifically, as shown in FIG. 2, a first moisture permeation suppressing layer 61 and a second moisture permeation suppressing layer 62 are provided along the outer peripheral portions of the first electrode portion 21 and the second electrode portion 22, respectively. Is preferred. Thereby, the friction between the water permeation suppression layer and the skin of the living body can suppress the displacement of the living body electrode even when the body movement is large, etc., making it difficult for the artifact to be taken in the bioelectric signal. It becomes possible to obtain the electrical signal with higher accuracy.

  When the water permeation suppression layer is provided along the outer peripheral portion of the electrode portion, the water permeation suppression layer is preferably made of an elastic member from the viewpoint of more effectively suppressing the displacement of the biological electrode. preferable. Specific examples of the elastic member include, for example, a sheet material made of rubber or resin; a fiber structure made of any one of a knitted structure, a woven structure, and a non-woven structure. When the moisture permeation suppressing layer is formed of a sheet material or the like made of rubber or resin, it is advantageous in that it can improve the feel of the wearer's skin and prevent itching and aching as much as possible.

  When selecting an elastic member, it can be set as one judgment standard that the surface of a moisture permeation control layer has larger frictional resistance than the surface of an electrode part. That is, in the aspect in which the moisture permeation suppressing layer is provided along the outer peripheral portion of the electrode portion, by employing the moisture permeation suppressing layer having a large frictional resistance, the lateral displacement preventing action (slippage on the skin of the wearer) Stop is strengthened, and the stop condition for the skin of the wearer is further enhanced. As a factor to increase the frictional resistance of the water permeation suppressing layer, it is preferable to select one having a rough surface roughness. Further, when the surface roughness is rough, the elasticity in the thickness direction is made rich, and when the surface roughness is fine, it is effective to take measures such that the elasticity in the thickness direction is strong (hard).

  In the case where the moisture permeation suppressing layer is formed of a fiber structure, there is also a method of intentionally exposing the elastic yarn on the surface and then performing a heat setting treatment to increase the frictional resistance (grip effect). . In addition, instead of elastic yarn, a resin material or ink material that exhibits grip property is sprayed, applied, printed, imprinted (a method of permeating the inside of the fabric and exposing it to the side opposite to the imprinted surface in a scattered manner) It may be made to adhere by methods, such as).

  Furthermore, in the case of forming a moisture permeation suppressing layer by a resin sheet material, it is preferable to use a resin sheet material having adhesiveness as a material. Specifically, the moisture permeation suppressing layer can be formed of a sheet of polyurethane or silicon. Thus, the raw material which comprises a water permeation suppression layer is not specifically limited.

  In the embodiment in which the moisture permeation suppressing layer is provided along the outer peripheral portion of the electrode portion, the moisture permeation suppressing layer may be provided over the entire periphery of the outer peripheral portion of the electrode portion, It may be provided. For example, as shown in FIG. 2, the moisture permeation suppressing layer may be provided only on the outer peripheral portion of the electrode portion, and as shown in FIGS. 3 and 4, between the electrode portion and the sensor attachment portion It may be provided. In FIG. 3 and FIG. 4, the area of the water permeation suppression layer located under the electrode portion is larger than the area of the electrode portion, and as a result of the water permeation suppression layer being exposed to the outer peripheral portion of the electrode portion The aspect which the suppression layer is provided along the outer peripheral part of the electrode part is shown.

<Base layer>
In the biological electrode of the present invention, the electrode portion is preferably provided on the base material layer. FIG. 4 shows an aspect in which the first electrode portion 21 and the second electrode portion 22 are provided on the first base layer 71 and the second base layer 72, respectively. In the case where the biological electrode of the present invention has a moisture permeation suppression layer below the electrode portion, it is preferable to have a base material layer, a moisture permeation suppression layer, and an electrode portion in order from the sensor attachment portion. This makes it possible to enhance the shape stability and mechanical strength of the bioelectrode of the present invention.

  The material constituting the substrate layer is not particularly limited, but in terms of improving the adhesion of the bioelectrode to the skin, a material excellent in flexibility is preferable. As a raw material which comprises a base material layer, Preferably, rubber | gum, such as chloroprene rubber, etc. and resin, such as polyester, a polyurethane, polyethylene, are mentioned. The raw material which comprises a base material layer may be one type, and may be two or more types. From the viewpoint of improving the adhesion of the bioelectrode to the skin, when the base material layer is made of a resin, the resin is preferably in the form of a sponge.

  The substrate layer may be a single layer or multiple layers. Moreover, when a base material layer is a multilayer, the raw material which comprises each layer may be the same, and may differ.

  The thickness of the substrate layer is not particularly limited, but from the viewpoint of improving the adhesion of the bioelectrode to the skin while enhancing the shape stability and mechanical strength of the bioelectrode, it is preferably about 0.1 to 10 mm. More preferably, about 1-8 mm is mentioned.

  It does not restrict | limit especially as a method to laminate | stack each layer of a sensor attachment part, an electrode part, a water permeation suppression layer, and a base material layer, The method of providing a heat press, an adhesive layer, etc. are mentioned. As a condition of the heat press, for example, the heat press is preferably performed under the conditions of a temperature of about 80 to 200 ° C., a pressure of about 0.01 to 10 MPa, and a time of about 5 to 120 seconds.

  Moreover, as a method of providing an adhesive layer, a urethane non-woven fabric, a nylon non-woven fabric, etc. are arrange | positioned between each layer, for example, The method of making it thermocompression-bond, The method of using an adhesive agent is mentioned. The adhesive is not particularly limited, and known adhesives can be used. For example, polyurethane-based adhesives and adhesives such as modified silicone polymers can be used. When the adhesive layer is provided, the thickness of the adhesive layer is not particularly limited, and may be, for example, about 1 to 300 μm, more preferably about 10 to 200 μm.

  The bioelectrode of the present invention may further be provided with layers other than these layers, if necessary.

  The total thickness of the biological electrode of the present invention is not particularly limited, and may be, for example, about 0.01 to 20 mm, more preferably about 0.1 to 15 mm. If it is less than the lower limit value, the electrode part may be separated from the skin, and if it is too thick, the comfort may be impaired.

<Connector>
In the living body electrode of the present invention, a connector is disposed on the side of the sensor attachment portion not in contact with the living body. The connector is a member for fixing the bioelectric signal measuring device to the bioelectrode of the present invention and electrically connecting the electrode portion and the bioelectric signal measuring device. For example, the first electrode 31 for electrically connecting the bioelectric signal measuring device to the first electrode portion 21 and the second electrode portion 22 with the biological electrode 10 shown in FIG. The second connectors 32 for electrical connection are respectively provided on the side Y of the sensor attachment portion not in contact with the living body.

  As the connector, it is preferable to use a conventional member used for the attaching / detaching part of the clothes, such as a metallic dot button, a conductive wire fastener, a conductive surface fastener, etc., and the bioelectric signal measuring device can be easily detached when worn. Preferably, the sensor attachment portion is exposed to the side not in contact with the living body.

  The position of the connector is not particularly limited as long as the electrode unit is disposed on the biocontact surface side of the sensor attachment unit. In order to arrange the electrode unit on the side of the sensor attachment unit in contact with the living body and to arrange the connector on the side not in contact with the living body, either the connector or the wiring described later penetrates the sensor attachment unit. Need to be. Which of the connector and the wiring passes through the sensor attachment portion can be arbitrarily selected according to the form of the connector and the wiring.

  For example, in the case of using a metal dot button or a wire fastener as a connector, the metal dot button or the wire fastener inevitably penetrates the sensor attachment portion at the time of attachment, and the wiring does not necessarily penetrate the sensor attachment portion. FIG. 1 shows an aspect in which the first wiring 41 and the second wiring 42 pass through the sensor attachment portion 1 respectively.

  In the biological electrode 10, the first connector 31 and the second connector 32 and the bioelectric signal measurement device are joined via the separation portion S of the sensor attachment portion 1. That is, when the biological electrode 10 is worn, the bioelectric signal measuring device and the first connector 31 and the second connector 32 are connected so as to straddle the separation portion S engaged by the insulating engagement member 50. For this reason, the first connector 31 and the second connector 32 are arranged to fit the size of the bioelectric signal measurement device.

  As a distance (the shortest distance) between the first connector 31 and the second connector 32 in a state in which the separating portion S is engaged by an insulating engagement member 50 described later (a state where the bioelectric signal measuring device is joined), For example, about 1 to 15 cm, preferably about 1.5 to 10 cm can be mentioned. Below the lower limit, the connectors may physically interfere with each other. When the upper limit is exceeded, additional wiring may be required between the bioelectric signal measuring device and the connector.

  In the case of using a conductive surface fastener as the connector, for example, the conductive surface fastener is fixed by being sewn to the sensor attachment portion. The thread used for this sewing has conductivity, and in addition to passing the thread through the conductive surface fastener, the conductive surface fastener is further passed through the sensor attachment portion to the wiring, whereby the sensor surface is attached with the conductive surface fastener. At the same time, the conductive surface fastener and the wiring can be electrically connected with the conductive thread.

  As a thread having conductivity, a metal such as silver, copper, gold, stainless steel or the like is processed into a thin line to impart flexibility, and a thread configured as a thread, a plating of these metals on a fiber material, carbon fiber And those obtained by impregnating a conductive polymer into a fiber material.

  In the bioelectrode of the present invention, the surface of the connector may be coated with an insulating member. Thereby, the acquisition accuracy of the bioelectric signal when the sensor attachment portion or the clothing gets wet due to sweat or the like can be further enhanced. As an insulation member, the below-mentioned adhesive tape etc. are mentioned.

<Wiring>
In the biological electrode of the present invention, the wiring is a member for electrically connecting the electrode portion and the connector. In FIG. 1, the first wiring 41 electrically connects the first electrode portion 21 and the first connector 31, and the second wiring 42 electrically connects the second electrode portion 22 and the second connector 32. It shows how it is connected in

  As the wiring, a sensor attachment portion printed with a conductive polymer exemplified as an electrode portion, a sensor attachment portion with a film of a conductive resin attached, a conductive fiber structure sewn to a sensor attachment portion And the like.

  In the case of printing a conductive polymer as the wiring, the conductive polymer may be printed so that an electrical connection with the electrode portion can be obtained after the electrode portion is fixed to the sensor attachment portion. After printing the polymer, the electrode portion may be fixed to the sensor mounting portion so as to obtain an electrical connection with the conductive polymer.

  When a film of conductive resin is used as the wiring, after fixing the electrode portion to the sensor attachment portion, a film of conductive resin is attached to the sensor attachment portion so that electrical connection with the electrode portion can be obtained. Alternatively, after the film of the conductive resin is attached, the electrode portion may be fixed to the sensor mounting portion so as to obtain an electrical connection with the film of the conductive resin.

  Similarly, when using a conductive fiber structure as the wiring, the wiring may be fixed after the electrode part, or the wiring may be fixed before the electrode part, but when using the conductive fiber structure It is also possible to integrally form the electrode portion and the wiring.

  In the case where the conductive members constituting the electrode portion and the wiring are separately formed and connected, the narrow strip portion connected to the electrode portion is often distinguished from the wiring. In the case where the electrode portion and the wiring are formed as an integral conductive member, the portion used in direct contact with the living body on the surface side in contact with the living body is the portion not in direct contact with the electrode portion and the living body It may be distinguished from the wiring.

  When the wiring comes in contact with the living body, a shunt resistor is inserted into the signal path of the bioelectric signal acquired by the electrode unit, and the desired bioelectric signal input to the measuring apparatus is attenuated. Therefore, the wiring is disposed so as to penetrate the inside of the sensor attachment portion, or the wiring is covered with an insulating member or the like so as not to be in contact with the living body. Here, as an insulating member, an insulating adhesive tape etc. are mentioned, for example. The adhesive tape may be a nonporous film made of a synthetic resin such as polyurethane, polyester, nylon, etc. having a thickness of about 10 to 100 μm, a microporous film in which the periphery of the pores is made water repellent, voids between fibers are polyurethane, polyester, nylon, etc. What uses as a base material the film previously filled with the water-repellent and insulating resin of this. A waterproof tape in which an adhesive layer such as a hot melt is laminated on at least one side of the substrate is particularly preferable as the adhesive tape. By using the adhesive tape, it is also possible to fix the wiring to the sensor attachment portion.

<Shield member>
A shield member (not shown) made of a conductive mesh or the like as a countermeasure against disturbance waves from the outside such as static electricity generated due to rubbing between cloths of clothes, induction from an external electronic device or power supply device, etc. It is preferable to dispose an electrically insulating member (for example, a base material layer, a moisture permeation suppressing layer, etc.) between the wiring and the electrode part and the sensor attachment member. A shield member can preferably be provided between the attachment member of the bioelectrode and the substrate layer. In addition, if the biological electrode has a water permeation suppression layer, preferably, a shield layer can be provided between the attachment member and the water permeation suppression layer.

  In the bioelectrode according to the present invention, the shield member is preferably arranged such that the shield member itself or the conductive member drawn therefrom is in conductive contact with the living body. As a material used for the shield member, a known conductive material (for example, a urethane film having a conductive pattern printed thereon) capable of forming a conductive mesh or the like can be used. Moreover, as a shield member, a conductive fiber knit (knit), a conductive resin film, a metal foil, etc. can also be used.

<Insulating engagement member>
In the bioelectrode according to the present invention, the insulating engagement member is a member for engaging the separation portion of the sensor attachment portion. 1 and 5 to 8 show that the separation portion S is engaged by the insulating engagement member 50. FIG. The insulating engagement member 50 has an insulating property, and the insulating engagement member 50 and the separation portion S are portions where the first electrode portion 21, the first connector 31, and the first wiring 41 are disposed, The insulation with the portion where the second electrode portion 22, the second connector 32, and the second wire 42 are arranged is secured. Thus, when the sensor attachment portion or the clothing gets wet due to sweat or the like, it is effectively suppressed that a short circuit occurs between the first electrode portion 21 and the second electrode portion 22. It is possible to obtain bioelectric signals with high accuracy.

  The material constituting the insulating engaging member is not particularly limited as long as the insulating engaging member can be used as a member, and, for example, a metal whose surface is covered with an insulating synthetic resin or an insulating synthetic resin Etc.

  The shape of the insulating engagement member is not particularly limited as long as the separation portion can be engaged. For example, a fastener (zipper, chuck), hook, hook, hook, hook, button, snap, clip, buckle, socket , Clamp fasteners (such as alligator clips), locking cords, chains, and the like. The insulating engagement member may not be removable in a state in which the separation portion is engaged, and as such an insulating engagement member, a mode in which the separation portion is filled with an insulating film (a separation portion The insulating film filling the above becomes an insulating engaging member) and the like.

<Bioelectric signal measurement device>
The bioelectric signal measurement apparatus is an apparatus that measures, records, converts, transmits, etc., the bioelectric signal acquired by the electrode unit. A commercially available thing can be used as a bioelectric signal measurement apparatus. As a bioelectric signal measurement device, one having a display unit such as a measurement result, and one having a function of transmitting a measurement result etc. to an external terminal such as a smartphone are also known.

  As described above, when the biological electrode 10 is worn, the bioelectric signal measuring device and the first connector 31 and the second connector 32 are connected so as to straddle the separation portion S engaged by the insulating engagement member 50. . At this time, from the viewpoint of reducing the possibility of a slight short circuiting between the surface of the bioelectric signal measuring device and the first connector 31 and the second connector 32, the bioelectric signal measuring device is insulating. More preferably, it is covered by a member. As an insulating member which covers a bioelectrical signal measuring apparatus, the packaging bag etc. which were formed with the insulating synthetic fiber are mentioned, for example.

  Examples of bioelectric signals acquired by the bioelectrode of the present invention include electrocardiograms (electrocardiograms), electromyograms, electroencephalograms, heart rate fluctuations and the like.

[clothing]
The clothing of the present invention is obtained by immobilizing the bioelectrode of the present invention such that the above-mentioned electrode part is in contact with a living body. The details of the bioelectrode of the present invention fixed to the garment are as described above.

  6 to 8 show clothes in which the first electrode portion 21 and the second electrode portion 22 of the living body electrode 10 are in contact with the living body. In the clothing of FIG. 6, the separation portion S is formed to extend from the upper end to the lower end of the front of the clothing, and in the clothing of FIG. 7, the separation portion S extends from the upper end to the lower end of the front of the clothing. It is so formed that, in the garment of FIG. 8, the separating part S is formed between the upper end and the lower end of the front of the garment.

  The clothes include, for example, wear and the like. In addition, as the material of the fabric constituting the clothes, those used for ordinary clothes can be used, and for example, natural fiber materials such as cotton and wool, synthetic fiber materials such as polyester and nylon, etc. It can be used without limitation.

  The method for fixing the bioelectrode of the present invention to a garment is not particularly limited, and may be, for example, a method in which a urethane non-woven fabric, a nylon non-woven fabric, etc. are disposed therebetween for thermocompression bonding, or an adhesive may be used. You may sew on clothing.

  The form of the clothing can be appropriately designed according to the type of bioelectric signal to be acquired. For example, in the case of acquiring an electrocardiogram, a form such as an underwear in which a biological electrode is disposed on the chest close to the heart of a living body is preferable.

  The clothing in which the bioelectrode according to the present invention and the fabric are combined can be brought into close contact with the surface of the electrode unit as skin clothes to obtain a bioelectric signal. For example, when such clothing is worn, it can be used in various fields such as sports, health, medicine, entertainment, etc. by recording and analyzing the bioelectric signal acquired from the bioelectrode in real time.

  EXAMPLES Hereinafter, the present invention will be described in more detail by way of examples, but the present invention is not limited to the following examples.

<Manufacturing of bioelectrodes>
The biological electrodes of Examples 1-9 and Comparative Examples 1 and 2 were obtained by the following method. The configuration of each biological electrode is the position of the separation unit (front surface: that is, the front side when attached to the chest of a living body, and between the first electrode unit and the second electrode unit shown in FIG. 5 to FIG. ), Distance between separation parts, distance between connectors, distance between electrodes (shortest distance between first electrode part and second electrode part), length of each electrode, surface area of each electrode (area in contact with living body) The water permeation suppressing layer around the electrode portion was configured as shown in Table 1.

Example 1
As fibers forming a fiber knitted fabric (knit) constituting the electrode part and the wiring part, nylon / silver-plated fiber (nylon multifilament [trade name: AGposs] manufactured by Santsu Fujishi Kogyo Co., Ltd.) 70 dtex / 34 f and polyurethane A fiber (44 dtex, Mobylon (registered trademark, manufactured by Nisshinbo Textiles Co., Ltd.) R) was prepared. Using these fibers, milling and knitting were carried out with a circular knitting machine to produce an electrode portion and a wiring portion knitted fabric constituted of a fiber knitted fabric (knit). The mixing ratio of fibers at this time was 80.7% by mass of silver-plated fibers and 19.3% by mass of polyurethane fibers. Moreover, the degree was set to 40 courses / 0.5 inches and 30 wales / 0.5 inches. The obtained fiber knitted fabric is scoured (10 minutes at 60 ° C.), washed with water (5 minutes), dehydrated (3 minutes with a dehydrator), dried (1 min at 80 ° C.) using a treating solution of 1 g / L of scouring agent. Time), finish of the fabric (fixed to the mold and subjected to 130 ° C. (wet heat) for 10 minutes), the conductive knitted fabric to be an electrode portion and wiring (a knitted fabric in which the electrode portion and the wiring portion are integrated) , 800 μm).

  Next, as a moisture permeation suppression layer (urethane film Esmer URS (registered trademark, made by Nippon Mata Co., Ltd.) # 550 μm thick) is laminated on the portion of the obtained conductive knitted fabric to be the electrode (temperature 170) C., pressure 10 kN, heat pressing under conditions of 30 seconds, thickness after lamination is 500 μm, thickness of water permeation suppressing layer of biological electrode after lamination is as described in Table 1.), On the moisture permeation suppression layer, foamed polyurethane (Aerres BTG, manufactured by Achilles Co., Ltd., 3 mm thick) as a base material layer was laminated, and these were adhered. Here, a portion where the conductive knitted fabric and the base material layer were not adhered was used as a wiring. Two sets of laminates of the electrode part and the wiring, the moisture permeation suppression layer, and the base material layer having the same laminated structure are prepared, and the first electrode part and the first wiring, and the first moisture permeation suppression, respectively. A laminate A of a layer, a base material layer, a second electrode portion and a second wiring, a second moisture permeation suppressing layer, and a laminate B of a base material layer were obtained.

  On the other hand, prepare a stretchable belt material (2 mm in thickness) as a sensor attachment portion, and use a shielding member made of a urethane film printed with a conductive pattern of 1 mm grid on one side via a laminating adhesive. It laminated | stacked and heat-sealed the sensor attachment part and the shield member. In addition, as an adhesive for lamination, hot melt adhesion was carried out by heating at 140 ° C. using Espancione FF EDH 35 manufactured by KB Salen Co., Ltd.

  Next, laminates A and B are respectively laminated on the shield member formed on one surface of the sensor attachment portion via the laminating adhesive, and the laminates A and B, the sensor attachment portion, and The laminate of the shield member was heat-sealed to form a laminate in which the electrode portion and the wiring, the moisture permeation suppression layer, the base material layer, the shield layer, and the sensor attachment portion were sequentially laminated.

  Next, as shown in FIG. 5, the first connector and the second connector were attached to the side of the belt-shaped cloth opposite to the living body so as to be connected to each wire. In the obtained laminate, the living bodies of the first wiring and the second wiring were coated with a polyester patch.

  Next, in order to form a belt-shaped bioelectrode provided with a separation portion as shown in FIG. 5, the separation between the first electrode portion and the second electrode portion is provided together with the material of the belt. The Next, a metal engagement member (can; see FIG. 5) having an insulation coating was attached to the separation part to manufacture a bioelectrode. The total thickness of the bioelectrical bridge at the portion where each electrode portion was disposed was 8 mm.

(Example 2)
In the bioelectrode of Example 1, the separation part is attached to the front and back (i.e., the dorsal side when attached to the chest of a living body, in the position shown in FIG. 9), and the bioelectrode is the separation part between the front and back. Thus, the bioelectrode of Example 2 was obtained in the same manner as in Example 1 except that both were provided in the same length and at a position to be divided into two.

(Example 3)
The biological electrode of Example 1 is an example except that the length (direction of belt length) and surface area of each electrode portion (first electrode portion and second electrode portion) are reduced as shown in Table 1. In the same manner as in 1, the bioelectrode of Example 3 was obtained.

(Example 4)
The biological electrode of Example 1 is the same as Example 1 except that the distance between the electrode parts (the shortest distance between the first electrode part and the second electrode part) is increased as shown in Table 1. , The biological electrode of Example 4 was obtained.

(Example 5)
In the bioelectrode of the first embodiment, the first electrode portion is formed of a rectangular cloth provided with the shield member so as to form a rectangular bioelectrode 10 as shown in FIG. 6 instead of the belt-shaped cloth. A laminate A of a first wiring, a first moisture permeation suppressing layer, a base material layer, a second electrode portion and a second wiring, a laminate B of a second moisture permeation suppressing layer, and a base material layer A biological electrode in the form of a wear as shown in FIG. 6 was obtained in the same manner as in Example 1 except that the biological electrode 10 was stacked and made into a garment and sewn to a garment.

(Example 6)
In the biological electrode of Example 1, the biological electrode of Example 6 was obtained in the same manner as in Example 1 except that the water permeation suppressing layer was not provided.

(Example 7)
A bioelectrode according to Example 7 in the same manner as Example 1 except that in the bioelectrode according to Example 1, the distance between separation parts is narrowed to 0.05 cm and the thickness of the water permeation suppressing layer is 7 μm. I got

(Example 8)
In the bioelectrode of Example 1, the length and surface area of each electrode are as shown in Table 1, and the thickness of the water permeation suppressing layer is 100 μm, in the same manner as in Example 1 except for A bioelectrode was obtained.

(Example 9)
In the biological electrode of Example 1, the length and surface area of each electrode are those described in Table 1, and the thickness of the water permeation suppressing layer is 0.05 μm, in the same manner as in Example 1. Eight bioelectrodes were obtained.

(Comparative example 1)
In the bioelectrode of Example 1, as shown in FIG. 9, the separation part is provided on the back (in other words, on the dorsal side when attached to the chest of a living being, in the position shown in FIG. 9) instead of the front. A biological electrode of Comparative Example 1 was obtained in the same manner as Example 1 except for the above.

(Comparative example 2)
In the biological electrode of Example 1, the biological electrode of Comparative Example 2 was obtained in the same manner as in Example 1 except that the separation part was not provided.

<Evaluation of short circuit prevention function>
If the entire biological electrode gets wet with sweat, a short circuit will occur between the electrodes, causing a short circuit and the waveform can not be seen x, a case where it is not short circuited even if it gets wet and the heartbeat waveform continues to be taken ○ The state in which the entire biomedical electrode is wet with sweat means the extent to which the entire sensor attachment portion absorbs sweat and can be understood by touch that it is wet.

<Comfort evaluation>
The comfort at the time of wearing each living body electrode obtained above was evaluated by the following method. Evaluation criteria are as follows. The results are shown in Table 1.
○: There is little feeling of tightening.
×: I feel a strong feeling of tightening.

<Evaluation of heart rate measurement accuracy>
Each living body electrode obtained above was worn by the following method, and the heartbeat measurement accuracy in the state where the whole living body electrode got wet with sweat was evaluated. The state in which the entire biomedical electrode is wet with sweat means the extent to which the entire sensor attachment portion absorbs sweat and can be understood by touch that it is wet. Evaluation criteria are as follows. The results are shown in Table 1. Further, for reference, the heartbeat waveforms obtained by wearing the biological electrodes of Example 1 and Comparative Examples 1 and 2 are shown in FIGS. 10 to 12 (FIG. 10 shows Example 1, FIG. 11 shows Comparative Example 1 and FIG. 12). Is shown in Comparative Example 2).
:: Able to obtain a stable heartbeat waveform ×: Unstable heartbeat waveform

DESCRIPTION OF SYMBOLS 1 sensor attachment part 10 living body electrode 21 1st electrode part 22 2nd electrode part 31 1st connector 32 2nd connector 41 1st wiring 42 2nd wiring 50 insulating engagement member 61 1st moisture permeation suppression layer 62 2nd moisture Permeation suppression layer 71 first base material layer 72 second base material layer d separation distance S in separation portion separation portion W distance between first electrode and second electrode

Claims (7)

Sensor mounting area,
A first electrode unit and a second electrode unit disposed on the side of the sensor attachment unit in contact with the living body;
The first connector for electrically connecting a bioelectric signal measuring device disposed on the side of the sensor attachment portion not in contact with the living body with the first electrode portion, and the bioelectric signal measuring device, A second connector for electrically connecting to the two electrodes;
A first wire electrically connecting the first electrode portion and the first connector; and a second wire electrically connecting the second electrode portion and the second connector;
Equipped with
The sensor attachment portion includes a portion where the first electrode portion, the first connector, and the first wiring are disposed, and the second electrode portion, the second connector, and the second wiring. And a separation part separated from the
The first connector, the second connector, and the bioelectric signal measurement device are joined via the separation unit,
The separation unit is engaged by an insulating engagement member.   The bioelectrode according to claim 1, wherein a first moisture permeation suppression layer and a second moisture permeation suppression layer are provided along the outer peripheral portions of the first electrode portion and the second electrode portion, respectively.   The bioelectrode according to claim 2, wherein each of the first moisture permeation suppressing layer and the second moisture permeation suppressing layer is formed of an elastic member.   The bioelectrode according to any one of claims 1 to 3, wherein each of the first electrode portion and the second electrode portion is made of a fiber fabric.   The said 1st electrode part and the said 2nd electrode part are each provided on the 1st base material layer arrange | positioned at the said sensor attachment part, and a 2nd base material layer, The bioelectrode as described in.   The bioelectrode according to any of the preceding claims, which is in the form of a belt.   The garment according to any one of claims 1 to 5, wherein the first electrode unit and the second electrode unit are in contact with a living body, and the biological electrode according to any one of claims 1 to 5 is fixed.