WO2019130832A1

WO2019130832A1 - Biological information measurement electrode and method for manufacturing biological information measurement electrode

Info

Publication number: WO2019130832A1
Application number: PCT/JP2018/041219
Authority: WO
Inventors: 三森　健一; 佐藤　弘樹; 高橋　功; 真由子林田
Original assignee: アルプスアルパイン株式会社
Priority date: 2017-12-27
Filing date: 2018-11-06
Publication date: 2019-07-04
Also published as: JPWO2019130832A1

Abstract

A biological information measurement electrode comprising a part that can come into contact with a living organism, wherein, on the surface of the part, a plurality of grooves are formed and a conductive layer that contains a conductive polymer is formed.

Description

Electrode for measuring biological information and method of manufacturing electrode for measuring biological information

The present invention relates to a biological information measurement electrode and a method of manufacturing a biological information measurement electrode.

For example, an electrode (electrode for measuring biological information) for measuring biological information is used for measuring biological information such as brain waves, pulse waves, electrocardiograms, myoelectricity, body fat and the like. When measuring biological information, an electrode for measuring biological information is attached to a living body (skin) with hair or body hair, and an electrical signal related to biological information is obtained by the electrode for measuring biological information, and biological information (for example, brain waves) Etc).

When measuring biological information, it is important that the biological information measuring electrode is in stable contact with the living body. Therefore, various electrodes for measuring biological information have been proposed in order to enhance the stability of contact with a living body.

As one of such electrodes for measuring biological information, for example, by forming a conductive polymer film on the surface of the protrusion of the electrode, conductivity is provided to the protrusion to ensure conduction between the electrode and the living body. In addition, an electrode for detecting a biological signal has been proposed (for example, Patent Document 1).

Japanese Patent Application Laid-Open No. 2016-36642

Since the biological information measurement electrode is used in contact with a living body, it needs to be clean at the time of use. Therefore, every time the biological information measurement electrode is used, the biological information measurement electrode is cleaned in advance by wiping off the water, dirt and the like remaining on the surface of the electrode with a cleaning liquid such as alcohol.

However, the conductive polymer film used for the electrode of Patent Document 1 is easily worn. Therefore, if you wipe the surface of the protrusion repeatedly when wiping off the water droplets or dirt remaining on the surface of the protrusion of the electrode, the conductive polymer film may be worn away and part of the conductive polymer film may be peeled off There is sex. As a result, since the conductive polymer film remaining on the surface of the protrusion and the living body do not contact stably, it becomes difficult for the conductive polymer film and the living body to conduct. On the other hand, when a part of the conductive polymer film peels off, the surface of the exposed protrusion comes in contact with the living body. The contact resistance (contact impedance) generated between the projection of the electrode and the skin tends to be higher than the contact impedance generated between the conductive polymer film and the skin. Therefore, when contact of the conductive polymer film with the living body is slight, it may not be possible to stably measure biological information.

An aspect of the present invention aims to provide a biological information measurement electrode capable of stably measuring biological information.

The biological information measuring electrode according to an aspect of the present invention is a biological information measuring electrode having a region capable of being in contact with a living body, and a plurality of grooves are formed on the surface of the region, and the conductive high A conductive layer containing molecules is formed.

The biological information measurement electrode according to one aspect of the present invention can stably measure biological information.

It is a perspective view showing the appearance of the living body information measurement electrode concerning a 1st embodiment. It is another perspective view which shows the external appearance of the electrode for biometric information measurement which concerns on 1st Embodiment. It is another perspective view which shows the external appearance of the electrode for biometric information measurement which concerns on 1st Embodiment. It is a front view of a living body information measurement electrode concerning a 1st embodiment. FIG. 2 is a cross-sectional view taken along line II of FIG. It is explanatory drawing which shows an example of the cross section of the front end groove part of a front-end | tip part. It is explanatory drawing which shows an example of the cross section of the auxiliary | assistant groove part of the side of an electrode leg. It is a figure which shows an example which measures a test subject's brain waves using the test | inspection apparatus provided with the electrode for biological information measurement which concerns on 1st Embodiment. It is explanatory drawing which shows an example of the state which made the front-end | tip part of a base | substrate part contact the scalp via a conductive layer. It is an explanatory view showing the state where a part of electric conduction layer of a tip part wears. It is explanatory drawing which shows the state which the liquid hold | maintained by the front end groove part spreads. It is a perspective view which shows another example of the groove part formed in the one end part of an electrode leg. It is a perspective view which shows another example of the groove part formed in the one end part of an electrode leg. It is a perspective view which shows another example of the groove part formed in the one end part of an electrode leg. It is a perspective view which shows another example of the groove part formed in the one end part of an electrode leg. It is a perspective view which shows an example of the other structure of the electrode for biological information measurement. FIG. 17 is a cross-sectional view taken along the line II-II in FIG. It is a flowchart which shows the manufacturing method of the electrode for biometric information measurement which concerns on 1st Embodiment. It is a figure which shows an example of the state by which the raw material supply channel | path is being fixed to the terminal part. It is a flowchart which shows another example of the manufacturing method of the electrode for biological information measurement. It is a flowchart which shows the manufacturing method of the electrode for biological information measurement which concerns on 2nd Embodiment. It is a flowchart which shows another example of the manufacturing method of the electrode for biological information measurement. It is a figure which shows the measurement result of impedance. It is a figure which shows the measurement result of the impedance of Example 1-1 and 1-2. FIG. 16 is a diagram showing measurement results of impedance when the biological information measurement electrode of Example 2-1 is used. It is a figure which shows the measurement result of the impedance at the time of using the electrode for biological information measurement of Comparative Example 2-2. FIG. 17 is a view showing measurement results of time until the potential falls to 300 kΩ or less when using the electrodes for biological information measurement of Examples 3-1 to 3-4 and Comparative Example 3-1. FIG. 16 is a view showing measurement results of time until the potential drops to 300 kΩ or less when using the electrodes for measuring biological information of Examples 4-1 to 4-18 and Comparative Example 4-1. FIG. 16 is a graph showing measurement results of resistance when using the electrodes for measuring biological information of Examples 5-1 and 5-2 and Comparative Example 5-1.

Hereinafter, embodiments of the present invention will be described in detail. In addition, in order to make an understanding of description easy, the same code | symbol is attached | subjected with respect to the same component in each drawing, and the overlapping description is abbreviate | omitted. In addition, the scale of each member in the drawings may be different from the actual one. In this specification, using a three-dimensional orthogonal coordinate system in three axial directions (X-axis direction, Y-axis direction, Z-axis direction), the direction parallel to the central axis J of the biological information measurement electrode is taken as the Z-axis direction. In the plane orthogonal to the axis J, one of two directions orthogonal to each other is taken as an X-axis direction, and the other as a Y-axis direction. In the following description, the + Z axis direction may be referred to as the upper side, and the −Z axis direction may be referred to as the lower side.

First Embodiment
<Electrode for measuring biological information>
The biological information measurement electrode according to the first embodiment will be described. In the present embodiment, as an example, measurement of biological information will be described by bringing an electrode for measuring biological information into contact with a scalp or a forehead that is a part of a living body. The electrode for measuring biological information according to the present embodiment may be any electrode for measuring biological information by bringing it into contact with a part of a living body. It may be a measure of The living body means a human body or a living thing other than the human body.

FIG. 1 is a perspective view showing the appearance of the biological information measurement electrode according to the present embodiment, and FIGS. 2 and 3 are other perspective views showing the appearance of the biological information measurement electrode according to the present embodiment. 4 is a front view of the biological information measuring electrode according to the present embodiment, and FIG. 5 is a cross-sectional view taken along the line II in FIG. FIG. 6 is an explanatory view showing an example of the cross section of the tip groove portion of the tip portion of the electrode leg, and FIG. 7 is an explanatory view showing an example of the cross section of the auxiliary groove portion on the side surface of the electrode leg. 1 to 5 indicate the central axis J of the biological information measurement electrode. The central axis J is an axis at the center when the biological information measurement electrode is installed on a living body.

The biological information measuring electrode 10 according to the present embodiment is provided on the base portion 20 having the base portion 21 and the plurality of electrode legs 22 and on the upper side (+ Z axis direction) of the base portion 21 as shown in FIGS. The terminal portion 30 and the conductive layer 40 provided on the surface of the electrode leg 22 are configured.

As a material for forming the base portion 20 and the terminal portion 30, a conductive elastomer or an insulating material can be used. Note that the insulating material refers to a material which does not have conductivity or which has extremely low conductivity. The base portion 20 and the terminal portion 30 may be formed of the same material or may be formed of different materials. In the present embodiment, the base portion 20 and the terminal portion 30 are integrally formed of the same conductive elastomer. Accordingly, the terminal portion 30 is electrically connected to the tip end portion 221 (described later) of the electrode leg 22.

The type of the conductive elastomer is not particularly limited. The conductive elastomer is obtained, for example, by melt mixing the conductive filler and the nonconductive elastomer. The base portion 20 and the terminal portion 30 have a low elastic modulus by being molded including a nonconductive elastomer having rubber elasticity. Therefore, at the time of use of the electrode 10 for measuring biological information, since the base 20 and the terminal 30 are easily deformed into the uneven shape of the scalp and forehead, contact with the scalp and forehead can be ensured, and pressing on the scalp and forehead It can relieve pressure.

The type of the conductive filler described above is not particularly limited as long as it has conductivity. For example, as the conductive filler, carbon materials such as graphite, carbon black, carbon nanotubes, carbon nanohorns or carbon fibers (carbon fibers); aluminum, gold, silver, copper, iron, platinum, chromium, tin, indium, antimony, Examples thereof include metals such as titanium and nickel; and conductive ceramics such as a so-called ABO ₃ type perovskite-type composite oxide, but the present invention is not limited thereto. These conductive fillers may be used alone or in combination of two or more. From the viewpoint of durability, it is preferable to use a carbon material.

Examples of the above-mentioned non-conductive elastomers include silicone rubber, ethylene propylene rubber, ethylene propylene diene rubber, isoprene rubber, butadiene rubber, styrene butadiene rubber, nitrile rubber, chloroprene rubber, acrylonitrile nitrile butadiene rubber, butyl rubber, urethane rubber, or Fluororubber etc. are mentioned. These may be used alone or in combination of two or more. Among these, in terms of durability and the like, it is preferable to use silicone rubber.

Moreover, as the insulating material which is not a conductive elastomer, the above non-conductive elastomer, polypropylene (PP), polycarbonate (PC), ABS resin, polyethylene terephthalate (PET), polybutylene terephthalate (PBT), polyamide (PA) or A liquid crystal polymer (LCP) or the like can be used.

[Substrate]
The base 20 has a base 21 and a plurality of electrode legs 22 as shown in FIGS.

The base 21 is formed in a substantially circular shape in a plan view (when viewed from the + Z axis direction). The base 21 has a projecting portion 211 on the back surface (−Z axis direction side) of the base 21. A plurality of (eight in FIGS. 1 to 5) projecting portions 211 are provided on the back surface of the base 21 and are disposed in an annular shape. An electrode leg 22 is integrally formed at an end of the protruding portion 211. The number of projecting portions 211 is designed to match the number of electrode legs 22. In addition, the structure which the electrode leg 22 formed continuously with the base 21 of a disc part may be sufficient, without providing the protrusion part 211. FIG.

The electrode leg 22 is extended from the projecting portion 211 of the base 21 in the −Z axis direction. The electrode leg 22 is formed in a cylindrical shape, and has a tip 221 capable of contacting the scalp at its tip. The distal end portion 221 is formed in a curved shape having a rounded end, and in the present embodiment, is formed in a dome shape. The shape of the tip portion 221 may be a rounded conical shape as another curved surface shape, or may be a flat shape having an end face that can be in contact with the scalp.

The tip portion 221 is a portion formed in a dome shape, and the tip which comes in contact with the scalp as a living body and the tip which may come in contact with the living body when the electrode 10 for measuring biological information is inclined. It means the surrounding area of In the present embodiment, the tip end portion 221 is referred to as “a region A capable of being in contact with a living body (hereinafter, referred to as“ a region A ”)”.

Further, the electrode leg 22 includes a groove (tip groove portion) 24A provided in the tip end portion 221 which is the region A, and an auxiliary groove portion (side groove portion) 25 which is provided in the side surface 222 of the electrode leg 22 which is a portion other Have. The electrode leg 22 can hold the liquid containing water in the tip groove 24A and the side groove 25 by providing the tip groove 24A and the side groove 25.

The liquid contained in the tip groove 24A and the side groove 25 may be any liquid other than water as long as it is a liquid such as an electrolytic solution (saline solution) which does not harm the living body.

The front end groove 24 A is formed on the surface of the front end 221 of the electrode leg 22. In the present embodiment, four tip groove portions 24A are formed radially at equal angles so as to form a cross shape when the tip portion 221 of the electrode leg 22 is viewed from the tip portion 221 in the + Z axial direction.

Further, as shown in FIG. 6, the cross-sectional shape of the tip groove portion 24A is formed in a substantially U shape in a cross-sectional view. In addition, the cross-sectional shape of tip groove part 24A may be formed in the substantially V shape in the cross sectional view.

The width W1 (see FIG. 6) of the tip groove 24A is preferably 10 μm to 450 μm. If the width W1 of the tip groove 24A is in the above range, the liquid can be held in the tip groove 24A even after the conductive layer 40 is formed in the tip groove 24A. In addition, if the conductive layer 40 is formed in the tip groove 24A, for example, even if the tip 221 of the electrode leg 22 is strongly wiped with a Kimwipe containing alcohol, the Kimwipe fibers enter the tip groove 24A. Can be reduced. In addition, if the width W1 is within the above range, since the width is smaller than the average thickness of the hair, the penetration of the hair into the tip groove 24A can be reduced. The width W1 of the tip groove portion 24A is more preferably 20 μm to 120 μm, still more preferably 30 μm to 70 μm, and most preferably 40 μm to 50 μm.

In the present embodiment, the width W1 refers to the maximum value (maximum width) of the width from the bottom of the tip groove 24A to the surface side. Even when the cross-sectional shape of the tip groove 24A is formed in a substantially V-shape in a cross-sectional view, the width W1 refers to the maximum width, that is, the value of the width on the surface of the tip 221.

The maximum depth H1 (see FIG. 6) of the tip groove 24A is preferably 10 μm to 500 μm. If the maximum depth H1 of the end groove 24A is in the above range, the end groove 24A can have a predetermined depth even if the conductive layer 40 is formed on the end 221 of the electrode leg 22. The maximum depth H1 of the tip groove 24A is more preferably 20 μm to 300 μm, and still more preferably 30 μm to 150 μm.

As shown in FIGS. 1 to 5, a plurality of side grooves 25 are formed on the surface of the side surface 222 of the electrode leg 22, which is a portion other than the tip 221, communicating with at least a part of the tip groove 24A. There is.

Further, the width W2 (see FIG. 7) of the side surface groove 25 is preferably 10 to 120 μm, similarly to the width W1 of the tip groove 24A. If the width W2 of the side surface groove 25 is 10 to 120 μm, even if the conductive layer 40 is formed in the side surface groove 25, the liquid can be held in the side surface groove 25. Also, if the conductive layer 40 is formed in the side groove 25, for example, even if the side 222 of the electrode leg 22 is strongly wiped with a Kimwipe containing alcohol, the Kimwipe fibers enter into the side groove 25. It can be reduced. In addition, when the width W2 is in the above range, the hair does not exceed the thickness of the hair, so that the penetration of the hair into the side groove 25 can be reduced. The width W2 of the side face groove 25 is more preferably 20 to 70 μm, and still more preferably 30 to 50 μm. In addition, since the definition of the width W2 of the side surface groove part 25 is the same as the above-mentioned width W1, description is abbreviate | omitted.

Further, the maximum depth H2 (see FIG. 7) of the side surface groove 25 is preferably 10 to 500 μm, similarly to the tip groove 24A. If the maximum depth H2 of the side surface groove 25 is within the above range, even if the conductive layer 40 is formed on the side surface 222 of the electrode leg 22, the tip groove 24A can have a predetermined depth. The maximum depth H2 of the tip groove 24A is more preferably 20 to 300 μm, and still more preferably 30 to 150 μm.

[Terminal]
The terminal portion 30 is an upper surface of the base portion 21 of the base portion 20 as shown in FIGS. 1 to 5 and protrudes in the + Z-axis direction from a substantially central portion of the base portion 21 (a position through which the central axis J passes) in plan view. Is provided. A metal layer 31 is provided at the central portion of the terminal portion 30. The conducting wire 52 of the inspection apparatus mentioned later is connected to the part in which this metal layer 31 was provided (refer FIG. 8). Thus, since the terminal portion 30 is electrically connected to the base portion 20 in which the electrode leg 22 is integrally formed, the terminal portion 30 and the tip portion 221 which is the region A of the electrode leg 22 are electrically connected. Thus, the biological information signal (electrical signal) from the area A can be extracted. Although metal such as gold, silver, or copper is preferably used as the metal layer 31, a layer made of a material having conductivity other than metal may be provided in the central portion of the terminal portion 30. Good.

Moreover, although the terminal part 30 is mentioned later, it is connected with the measurement part 53 (refer FIG. 8). Specifically, the terminal portion 30 is connected to a conducting wire 52 (see FIG. 8) or the like, and the conducting wire 52 (see FIG. 8) and the measuring unit 53 (see FIG. 8) are connected. The terminal unit 30 transmits a biological information signal (electric signal) from the scalp obtained from the tip end portion 221 of the electrode leg 22 through the base unit 20 to the measurement unit 53 (see FIG. 8), and biological information (for example, an electroencephalogram) Measured as).

[Conductive layer]
The conductive layer 40 is provided on the surface of the tip end portion 221 of the electrode leg 22. In the present embodiment, since the base portion 20 and the terminal portion 30 are integrally formed using a conductive elastomer, the conduction between the base portion 20 and the terminal portion 30 is secured. Therefore, the conductive layer 40 is formed only on the surface of the tip portion 221. When base portion 20 and terminal portion 30 are formed of an insulating material, conductive layer 40 ensures the entire surface of base portion 20 and terminal portion 30 to ensure conduction between base portion 20 and terminal portion 30. Provided in

The conductive layer 40 also contains a conductive polymer. As the conductive polymer, for example, PEDOT / PSS, polyacetylene, polyaniline, polythiophene, polythiophene, polyphenylene in which polystyrene sulfonic acid (poly 4-styrene sulfonate; PSS) is doped to poly3,4-ethylenedioxythiophene (PEDOT) Vinylene or polypyrrole can be used. Among them, it is preferable to use PEDOT / PSS in view of lower contact impedance with a living body and high conductivity.

The average thickness of the conductive layer 40 is preferably 3 to 5 μm. If it is in this range, it can have conductivity, and can electrically conduct the electric signal transmitted from the scalp stably. The average thickness of the conductive layer 40 refers to the average value of the thickness of the conductive layer 40. For example, in the cross section of the conductive layer 40, when several places (for example, about six places) are measured in arbitrary places, the average value of the thickness of these measurement places is said. Further, in the present embodiment, the thickness refers to the length of the layer in the direction perpendicular to the contact surface of the conductive layer 40.

Next, an example in the case of measuring an electroencephalogram of a subject using an inspection apparatus provided with the biological information measurement electrode 10 according to the present embodiment will be described. FIG. 8 is a view showing an example of measuring an electroencephalogram of a subject using an inspection apparatus provided with the biological information measuring electrode 10. As shown in FIG. FIG. 9 is an explanatory view showing an example of a state in which the tip end portion 221 of the base portion 20 is in contact with the scalp 55 via the conductive layer 40. As shown in FIG. FIG. 10 is an explanatory view showing a state in which a part of the conductive layer 40 of the tip end portion 221 is worn. FIG. 11 is an explanatory view showing a state in which the liquid held by the end groove 24A spreads.

As shown in FIG. 8, the inspection apparatus 50 includes the biological information measurement electrode 10, a cap 51 that covers the head of the subject, a lead 52, a measurement unit 53, and a display unit 54. The cap 51 has the shape of a hat or a helmet so as to cover the subject's head, and is formed of synthetic resin, cloth or the like. The biological information measuring electrodes 10 are provided at a plurality of locations (for example, 21 locations) on the cap 51 at predetermined intervals, and are attached to an arbitrary location of the scalp 55 of the subject. The conducting wire 52 is, for example, a lead wire, and one end is connected to the terminal unit 30 and the other end is connected to the measuring unit 53. The measurement unit 53 includes a power supply unit 531 and a signal analysis unit 532 that analyzes an electrical signal and measures an electroencephalogram as biological information. The display unit 54 is a monitor and displays the electroencephalogram 541 analyzed by the signal analysis unit 532. The brain waves 541 are classified into, for example, α wave (8 to 13 Hz), β wave (14 to 30 Hz), θ wave (4 to 7 Hz), and δ wave (0.5 to 3 Hz) according to the frequency.

In the biological information measuring electrode 10, at least the tip portion 221 of the electrode leg 22 is previously dipped in the liquid in the container, and the tip groove portion 24A of the conductive layer 40 and the side groove portion 25 contain the liquid. Even when the electrode leg 22 is pulled up from the immersion state in the liquid, the liquid is held in the tip groove 24A and the side groove 25 by capillary action. Thereafter, the distal end groove portion 24A and the side surface groove portion 25 are fixed to the cap 51 in a state of containing the liquid, thereby contacting the distal end portion 221 of the electrode leg 22 with the scalp 55 via the conductive layer 40 as shown in FIG. Let

When the power supply unit 531 is inserted and measurement is started, an electrical signal from the scalp is transmitted from the scalp 55 to the tip portion 221 of the electrode leg 22 through the conductive layer 40. The transmitted electric signal is transmitted from the tip end portion 221 through the base portion 20 in the order of the terminal portion 30, the lead 52, and the measuring portion 53. The signal analysis unit 532 analyzes the transmitted electric signal, and displays an electroencephalogram (for example, an α wave, a β wave, a θ wave, etc.) 541 on the display unit 54.

The biological information measuring electrode 10 configured as described above has a plurality of tip grooves 24A on the surface of the tip 221 which is the region A, and the conductive layer 40 on the surface of the tip 221. By repeatedly using the biological information measuring electrode 10, for example, as shown in FIG. 10, a state in which a part of the conductive layer 40 on the surface of the tip part 221 is gradually worn away and the tip part 221 is partially exposed. There is a possibility that part of the conductive layer 40 may be peeled off until Even in such a case, in the biological information measuring electrode 10, the conductive layer 40 formed on the surface of the tip groove 24A remains. Therefore, since the conduction of the conductive layer 40 can be maintained at the contact portion between the conductive layer 40 formed on the surface of the tip groove 24A and the scalp, the conduction between the conductive layer 40 and the scalp can be stably maintained. Therefore, according to the electrode 10 for measuring biological information, since the electrical connection between the tip portion 221 of the electrode leg 22 and the scalp can be maintained, an electrical signal from the scalp can be stably obtained, and an electroencephalogram can be obtained as biological information. It can be measured stably.

In addition, the biological information measuring electrode 10 has the conductive layer 40 on the surface of the tip portion 221, so that it is more between the scalp and the biological information measuring electrode 10 than when the tip portion 221 is in direct contact with the scalp. Can reduce the contact impedance of

Furthermore, when the biological information measuring electrode 10 is immersed in the liquid, the liquid can be held by capillary action in the tip groove 24A provided on the surface of the tip portion 221 which is the region A. Therefore, when measuring the electroencephalogram, when the tip end portion 221 is brought into contact with the scalp, as shown in FIG. 11, the liquid held in the tip groove portion 24A flows on the surface of the scalp in contact with the tip end portion 221 to the scalp. spread. As a result, the area of conduction from the scalp to the conductive layer 40 is increased, so the contact impedance between the scalp and the biological information measuring electrode 10 can be further lowered. Thereby, the electroencephalogram can be measured more stably.

The biological information measuring electrode 10 has a plurality of side grooves 25 on the side surface of the electrode leg 22, and the side grooves 25 communicate with at least a part of the tip groove 24A. Therefore, at the time of measurement of the electroencephalogram, the liquid held in the tip groove 24A flows to the surface of the scalp in contact with the tip 221, and the liquid held in the tip groove 24A is consumed. At this time, the liquid held in the side groove 25 flows to the tip groove 24A and is supplied to the scalp. Thereby, the contact between the scalp and the biological information measuring electrode 10 can be maintained while the contact impedance between the scalp and the biological information measuring electrode 10 is kept low, so that the biological information can be continued more stably. Can be measured.

In addition, the electrode for measuring biological information formed of metal can not be used for a subject with metal allergy because the contact surface of the electrode with the subject is metal and may cause metal allergy to the subject. . In the present embodiment, since the conductive layer 40 is formed to contain a conductive polymer, even if the conductive layer 40 contacts the scalp, it does not cause metal allergy to the subject, which is safe. Therefore, the biological information measurement electrode 10 can be used with confidence for all subjects.

[Modification]
Although an example of the biological information measurement electrode 10 is shown, the present invention is not limited to this. Hereinafter, some modifications of the biological information measuring electrode 10 will be described.

In the present embodiment, the tip groove portion 24A is radially formed on the tip portion 221 so as to become a cross shape when the tip portion 221 of the electrode leg 22 is viewed in the + Z axial direction, but the tip groove portion 24A is And any shape that can hold the liquid in the groove. For example, as shown in FIG. 12, when the tip end portion 221 of the electrode leg 22 is viewed in the + Z axial direction, six tip groove portions 24B may be formed at the same angle in the radial direction. Further, as shown in FIG. 13, when the tip end portion 221 of the electrode leg 22 is viewed in the + Z axial direction, the tip end portion 221 may be provided with a tip end groove portion 24C formed in a mesh shape. Furthermore, as shown in FIG. 14, a distal end groove 24D formed in a dendritic shape may be provided. As shown in FIG. 12 to FIG. 14, even when the distal end groove portion 24B formed radially, the distal end groove portion 24C formed in a mesh shape, or the distal end groove portion 24D formed in a dendritic shape are provided in the distal end portion 221, The liquid can be more efficiently held in the tip grooves 24B to 24D on the surface of the tip 221. Therefore, the conduction between the conductive layer 40 and the scalp can be maintained more stably. In addition, when the tip end portion 221 contacts the scalp, the tip end portion 221 can stably maintain the conduction between the conductive layer 40 on the surface of the tip end groove portions 24B to 24D and the scalp in any direction. Therefore, biological information can be measured more stably even if the tip 221 is moved in any direction along the scalp.

In the present embodiment, the distal end groove portion 24A is formed in the distal end portion 221 of the electrode leg 22, but as shown in FIG. 15, the recessed portion 26 may be formed in the distal end portion 221 of the electrode leg 22. Even when the recessed portion 26 is provided in the tip end portion 221, the liquid can be more efficiently held in the recessed portion 26 in the surface of the tip end portion 221, so that the conduction between the conductive layer 40 and the scalp can be maintained more stably. . In addition, when the tip end portion 221 contacts the scalp, the tip end portion 221 can stably maintain conduction between the conductive layer 40 on the surface of the depression portion 26 and the scalp in all directions. Therefore, biological information can be measured more stably even if the tip portion 221 is moved in any direction along the scalp.

The width of the recess 26 is preferably 10 μm to 450 μm, more preferably 20 μm to 120 μm, still more preferably 30 μm to 70 μm, and most preferably 40 μm to 50 μm, as in the tip groove 24A. The reason why the width of the recess 26 is preferably 10 μm to 450 μm is the same reason as the tip groove 24A. In addition, the width | variety of the hollow part 26 is a diameter in planar view of a front end, when the hollow part 26 is circular. If the recess 26 is elliptical, it is the diameter of the tip in plan view. The average value of the major and minor axes of the recess 26 is taken as the width of the recess 26.

The maximum depth of the recess 26 is preferably 10 μm to 500 μm, more preferably 20 μm to 300 μm, and still more preferably 30 μm to 150 μm, as in the tip groove 24A. The reason why the maximum depth of the recess 26 is preferably 10 μm to 500 μm is the same reason as the tip groove 24A.

In the present embodiment, the base portion 20 and the terminal portion 30 are integrally formed, but the base portion 20 and the terminal portion 30 may be configured by separate members. One example of the biological information measuring electrode 10 when the base portion 20 and the terminal portion 30 are constituted by separate members is shown in FIG. 16 and FIG. FIG. 16 is a perspective view showing an example of another configuration of the biological information measuring electrode 10, and FIG. 17 is a cross-sectional view taken along the line II-II of FIG. As shown in FIGS. 16 and 17, the terminal portion 30 has a disc-shaped base portion 301 and a convex portion 302 protruding from the central portion of the base portion 301. The terminal portion 30 is formed of a conductive material such as a metal material. The terminal portion 30 is fixed and connected to an end portion 21a opposite to the side where the base portion 21 of the base portion 20 is continuous with the electrode leg 22, for example, with a conductive adhesive or conductive paste (not shown). It is done. Thus, the terminal portion 30 is electrically connected to the base portion 20 formed integrally with the electrode leg 22. Therefore, the tip end portion 221 of the electrode leg 22 is electrically connected to the terminal portion 30 via the base portion 21 of the base portion 20.

In the present embodiment, the base portion 20 integrally forms the base portion 21 and the electrode leg 22, but the base portion 21 and the electrode leg 22 may be configured by separate members. At this time, the base 21 and the electrode leg 22 are bound by a binding member made of synthetic resin. The binding member is one obtained by curing a synthetic resin such as an epoxy resin or a urethane resin. In addition to the synthetic resin, the binding member may be an elastic synthetic resin such as rubber.

In the present embodiment, the side surface groove 25 is formed on the surface of the side surface 222 of the electrode leg 22. However, the side surface groove 25 is not formed if the tip groove 24A can sufficiently hold the liquid. May be

The conductive layer 40 is formed at the tip end portion 221 of the electrode leg 22 which is the region A, but may be formed at another portion of the base portion 20 as long as it is formed at least at the tip end portion 221. Alternatively, it may be formed on the entire surface of the base portion 20 and the terminal portion 30. For example, when the base portion 20 and the terminal portion 30 are formed of an insulating material, forming the entire surface of the base portion 20 and the terminal portion 30 further stabilizes the conduction from the tip portion 221 to the terminal portion 30. be able to.

<Manufacturing method of biological information measuring electrode according to the first embodiment>
Next, a method of manufacturing the biological information measuring electrode according to the first embodiment will be described. FIG. 18 is a flowchart showing a method of manufacturing the biological information measuring electrode according to the present embodiment. FIG. 19 is a view showing an example of a state where the raw material supply passage 61 used at the time of molding is fixed to the terminal portion 30. As shown in FIG.

In the method of manufacturing the biological information measuring electrode according to the present embodiment, as shown in FIG. 18, the base portion 20 and the terminal portion 30 are formed, and a plurality of tip grooves 24A are formed on the surface of the tip portion 221 which is the region A. Forming step (step S11) for forming the side groove portion 25 on the side surface 222, surface treatment step (step S12) for activating the surface of the tip portion 221, and conductive polymer on the surface of the tip portion 221 And a conductive layer forming step (step S13) of forming a conductive layer 40 containing Each step will be described below.

First, in the molding step (step S11), the base portion 20 and the terminal portion 30 are integrally molded using a material for forming the base portion 20 and the terminal portion 30, and a plurality of tip groove portions 24A are formed on the surface of the tip portion 221. To form the side grooves 25 on the side surface 222.

The base portion 20 and the terminal portion 30 are made of the base portion 20 and the terminal portion 30 having desired shapes by a known molding method such as compression molding (compression molding), injection molding (injection molding), or extrusion molding (transfer molding). It can be molded. When using these molding methods, a mold corresponding to the shapes of the base portion 20 and the terminal portion 30 is used. The mold is provided with a protrusion corresponding to the end groove 24A and the side groove 25. By using the mold, the base portion 20 and the terminal portion 30 can be simultaneously formed, and the tip groove 24A and the side surface groove 25 can be simultaneously formed.

In the case of using the injection molding method or the like, the raw material supply passage (e.g., a spool, a runner, etc.) to which the raw material (such as resin or metal) for molding the base portion 20 and the terminal portion 30 is supplied after injection molding. Or, it is connected to the terminal unit 30. For example, as shown in FIG. 19, when the raw material supply passage 61 is connected to the terminal portion 30, at least a part of the raw material supply passage 61 can be used for the terminal portion 30 even after the base portion 20 and the terminal portion 30 are formed. It is preferable to connect to When immersing at least a part of the base portion 20 and the terminal portion 30 in a solution containing a conductive polymer in the conductive layer forming step (step S13) described later, the raw material supply passage 61 serves as a grip for the base portion 20. It can be used as The raw material supply passage 61 is determined at which position of the product to perform suitable molding, and may be connected to the base 21 or the like of the base 20 other than the terminal 30 shown in FIG. .

Next, in the surface treatment step (step S12), the surface of the tip portion 221 is applied using a method of irradiating vacuum ultraviolet light (excimer UV light) by excimer or a method of plasma processing in a mixed gas containing Ar and oxygen. Activate the By performing the activation process on the surface of the tip portion 221, the adhesion between the tip portion 221 and the conductive layer 40 can be improved in the conductive layer forming step (step S13) described later. Thereby, when physical force is applied by washing | cleaning, wiping off, etc. of the front-end | tip part 221, it can prevent that the conductive layer 40 peels easily from the base | substrate part 20 (mainly front-end | tip part 221).

In addition, in the case of using a method of irradiating excimer UV light, the surface of the tip portion 221 is irradiated with excimer UV light. Excimer UV light is UV light having a wavelength of 240 nm or less in the atmosphere, and has a predetermined wavelength (central wavelength) depending on the type of discharge gas. As the dischargeable gas, Ar ₂ (wavelength 126 nm), Kr ₂ (wavelength 146 nm), ArBr (wavelength 165 nm), Xe ₂ (wavelength 172 nm), KrI (wavelength 191 nm), KrCl (wavelength 222 nm) or the like can be used. . A radiation lamp emitting excimer UV light is, for example, a dielectric barrier discharge lamp sealed with Xe gas. In this case, the dielectric barrier discharge lamp is in an excimer state (Xe ₂ ^* ) in which Xe atoms are excited, and generates light with a wavelength of about 172 nm when it dissociates again into Xe atoms from this excimer state. By irradiating the light of wavelength 172 nm to oxygen, high concentration ozone is generated. By the action of the ozone, the surface of the portion to which the excimer UV light is irradiated among the base portion 20 and the terminal portion 30 is modified, and a highly hydrophilic group (for example, a hydroxyl group (OH group), an aldehyde group (CHO group) Thus, a carboxyl group (COOH group) is formed, whereby the surface of the tip portion 221 of the base portion 20 can be activated, and the surface of the tip portion 221 can be made hydrophilic. The wettability to the liquid of the surface of tip part 221 can be improved.For this reason, only the tip part 221 can be activated easily by the method of irradiating excimer UV light, so the base part 20 and the terminal part 30 can be effectively used in the case where it is formed of a conductive material, It is sufficient if at least the surface of the tip portion 221 can be activated, 221 and portions other than may be irradiated with excimer UV light the entire base portion 20 and the terminal portion 30.

In addition, in the case of using the method of plasma treatment in a mixed gas containing Ar and oxygen, the entire surface of the base portion 20 and the terminal portion 30 is plasma activated. Thus, the entire surface of the base portion 20 and the terminal portion 30 can be changed to hydrophilicity in addition to the surface of the tip portion 221. As a result, the wettability to the liquid of the whole surface of base part 20 and terminal area 30 including tip part 221 can be improved. Therefore, even when the base portion 20 and the terminal portion 30 are formed of either a conductive material or an insulating material, it can be effectively used.

Finally, in the conductive layer forming step (step S13), the conductive layer 40 containing a conductive polymer is formed on the surface of the tip portion 221. The conductive layer forming step (step S13) includes a coating step (step S131) and a drying step (step S132).

In the coating step (step S131) of the conductive layer forming step (step S13), a solution containing a conductive polymer is applied to at least the tip portion 221 to form a coating layer. As a method of applying a solution containing a conductive polymer to at least the tip portion 221, an immersion method of immersing at least the tip portion 221 in a solution containing a conductive polymer, a solution containing a conductive polymer at least at the tip portion 221 A spray method or the like can be used.

In the drying step (step S132) of the conductive layer forming step (step S13), the applied layer formed on the tip portion 221 is dried to cure the applied layer. Thereby, the conductive layer 40 is formed on the surfaces of the tip end portion 221 and the tip end groove portion 24A. In the present embodiment, since the base portion 20 and the terminal portion 30 are formed of a conductive elastomer, the conductive layer 40 may be formed on the surface of the tip portion 221.

As described above, the conductive layer 40 is formed on the surface of the tip portion 221, whereby the biological information measurement electrode 10 is obtained. Therefore, by repeatedly using the biological information measurement electrode 10, the conductive layer 40 provided on the surface of the tip groove 24A remains even if the conductive layer 40 provided on the tip 221 is worn and scraped off. Therefore, since the conduction with the scalp can be maintained at the contact portion between the conductive layer 40 formed on the surface of the tip groove 24A and the scalp, the conduction between the conductive layer 40 and the scalp can be stably maintained. .

[Modification]
Although an example of the manufacturing method of the living body information measurement electrode concerning this embodiment was shown, it is not limited to this. Below, the modification in the manufacturing method of the electrode for biometric information measurement is demonstrated.

In the present embodiment, in the molding step (step S11), the base portion 20 and the terminal portion 30 are simultaneously formed using a mold provided with a protrusion corresponding to the tip groove portion 24A and the side surface groove portion 25. It is not limited. For example, the tip groove 24A and the side groove 25 may be formed after the base portion 20 and the terminal portion 30 are separately molded and integrated, respectively.

In this case, as shown in FIG. 20, in the method of manufacturing the biological information measuring electrode according to the present embodiment, the forming step (step S11) is a preparing step (step S111) of preparing the base portion 20 and the terminal portion 30. A bonding step of bonding and integrating the base portion 20 and the terminal portion 30 (step S112), and a groove forming step of forming the plurality of tip grooves 24A and the side grooves 25 on the surface of the tip portion 221 (step S113) And consists of. Then, as in the present embodiment, a surface treatment step (step S12) for activating the surface of the tip portion 221, and a conductive layer for forming a conductive layer 40 containing a conductive polymer on the surface of the tip portion 221. And a forming process (step S13).

In the binding step (step S112) of the above-described forming step (step S11), the base portion 20 and the terminal portion 30 are integrated using a binding member. A known binding member can be used as the binding member used for this binding. For example, synthetic resin such as epoxy resin or urethane resin, or synthetic resin having elasticity such as rubber can be used.

Further, in the present embodiment, in the conductive layer forming step (step S13), the conductive layer 40 is formed only at the tip end portion 221 of the base portion 20, but the conductive layer 40 is formed at least at the tip end portion 221. Preferably, the conductive layer 40 may be formed on the portion other than the tip end portion 221 of the base portion 20, or on the whole of the base portion 20 and the terminal portion 30. In the present embodiment, since the base portion 20 and the terminal portion 30 are formed of a conductive elastomer, the conductive layer 40 may be formed at least on the surface of the tip portion 221, but the base portion 20 and the terminal portion 30 are insulated. When formed of a material, the conductive layer 40 is formed on the entire surface of the base portion 20 and the terminal portion 30. Thereby, the electrical signal obtained from the scalp is transmitted from the tip end portion 221 of the electrode leg 22 to the terminal portion 30 through the conductive layer 40.

Second Embodiment
A biological information measurement electrode according to a second embodiment will be described. The biological information measuring electrode according to the present embodiment is the same as the first above except that the material for forming the base portion 20 and the terminal portion 30 of the biological information measuring electrode 10 according to the first embodiment is changed. Since it is the same as that of the electrode 10 for measuring biological information according to the embodiment of the present invention, only the configurations of the base portion 20, the terminal portion 30, and the conductive layer 40 will be described in the present embodiment. The configuration of the biological information measurement electrode according to the present embodiment will be described with reference to FIGS. 1 to 5 showing the biological information measurement electrode 10 according to the first embodiment.

[Base part and terminal part]
The base portion 20 and the terminal portion 30 of the biological information measuring electrode according to the present embodiment are formed of a resin material containing a carbon material, and the resin material is used as a matrix (matrix), and the carbon material is contained in the resin material. It is a composite material. The base portion 20 and the terminal portion 30 may be formed of the same material or may be formed of different materials. In the present embodiment, the base portion 20 and the terminal portion 30 are integrally formed of the same material by injection molding. Accordingly, the terminal portion 30 is electrically connected to the tip end portion 221 (described later) of the electrode leg 22.

A thermoplastic resin is suitably used as the above-mentioned resin material. The thermoplastic resin is not particularly limited, and, for example, polyamide (for example, nylon 6, nylon 66), polycarbonate, polyoxymethylene, polyphenylene sulfide, polyphenylene ether, polyester (for example, polyethylene terephthalate, polybutylene terephthalate, polyethylene naphthalate) And polyethylene, polypropylene, polystyrene, polymethyl methacrylate, AS resin and ABS resin. These may be used singly or in combination of two or more. As the thermoplastic resin, it is preferable to use polyamide, polycarbonate, polyphenylene sulfide, polyester, or polypropylene from the viewpoint of weatherability, moldability, strength, cost and the like.

The carbon material described above can impart conductivity to the base portion 20 and the terminal portion 30, and can make the base portion 20 and the terminal portion 30 lightweight and flexible. As the carbon material, graphite, carbon black, carbon nanotube, carbon nanohorn or carbon fiber (carbon fiber) or the like is used. Moreover, a carbon material may be used individually by 1 type, and may use 2 or more types together.

Further, among carbon materials, it is preferable to use a carbon fiber from the viewpoint of productivity, handleability, and cost. The carbon fiber is roughly divided into a PAN system and a pitch system due to the difference in starting materials, but any type may be used, and they may be used in combination. When a carbon fiber is used as the carbon material, one having an average thickness (average diameter) of about 5 μm to 10 μm and an average length of about 50 μm to 200 μm is preferably used. If the average diameter is in the range of 5 μm to 10 μm and the average length is in the range of 50 μm to 200 μm, the resin material can be easily dispersed. The thickness of the carbon fiber can be determined by a known measurement method using a light scattering device, a laser microscope, a scanning electron microscope (SEM) or the like. For example, a carbon fiber is observed with an SEM or the like, and a length in a direction orthogonal to the longitudinal direction of a predetermined number (for example, 10 to 200) of carbon fibers arbitrarily selected (a length in a radial direction of the carbon fiber The average diameter can be determined by measuring) and calculating the average value thereof.

The content ratio of the thermoplastic resin and the carbon material is preferably 10 parts by mass to 40 parts by mass, and 20 parts by mass to 30 parts by mass with respect to 100 parts by mass of the thermoplastic resin. More preferable. When the carbon material is 20 parts by mass to 30 parts by mass with respect to 100 parts by mass of the thermoplastic resin, the formability of the base portion 20 and the terminal portion 30 is improved and the shapes of the base portion 20 and the terminal portion 30 are It can be maintained stably.

[Conductive layer]
The conductive layer 40 is provided on the surface of the tip end portion 221 of the electrode leg 22. In the present embodiment, since the base portion 20 and the terminal portion 30 are integrally formed using a conductive composite material containing a carbon material in a resin material, the conduction between the base portion 20 and the terminal portion 30 is secured. ing. Therefore, the conductive layer 40 is formed only on the surface of the tip end portion 221 (a portion corresponding to the region A). When the base portion 20 and the terminal portion 30 other than the region A are formed of an insulating material, the conductive layer 40 ensures conduction between the base portion 20 including the region A and the terminal portion 30, It is provided on the entire surface of the base portion 20 and the terminal portion 30.

In the biological information measurement electrode according to the present embodiment, the base portion 20 including the tip portion 221 and the terminal portion 30 are formed of a resin material including a carbon material. Therefore, the biological information measurement electrode according to the present embodiment can be made lighter and more flexible. When a metal film is formed on the surface of the protrusion of the biological information measurement electrode as in the conventional biological information measurement electrode, the metal film is heavier than the conductive polymer film etc. When worn on the head, etc., it may give a feeling of weight and give the subject a sense of tension. On the other hand, in the biological information measurement electrode according to the present embodiment, since the base portion 20 and the terminal portion 30 can be formed of a resin material containing a carbon material, and can be made lighter and more flexible, according to the present embodiment. Even when the biological information measurement electrode is attached to the head of the subject, it is possible to reduce the weight feeling. Thereby, it is possible to measure an electroencephalogram as biological information without giving a subject a certain sense of tension or the like. In the present embodiment, the biological information measuring electrode according to the present embodiment can be made lighter by, for example, 56% than an electrode of the same size in which the base portion is formed of metal and the surface is gold-plated.

Further, in the biological information measurement electrode according to the present embodiment, as described in the biological information measurement electrode 10 according to the first embodiment, the conductive layer 40 is formed to include the conductive polymer. . Therefore, even if the conductive layer 40 contacts the scalp, it does not cause metal allergy to the subject, which is safe. Therefore, the biological information measurement electrode according to the present embodiment can be used with confidence for all subjects.

[Modification]
Although an example of the biological information measurement electrode according to the present embodiment is shown, the present invention is not limited to this. Hereinafter, modified examples of the biological information measurement electrode according to the present embodiment will be described.

In the present embodiment, a thermoplastic resin is used as the resin material for the base portion 20 and the terminal portion 30. However, a resin material other than a thermoplastic resin such as a nonconductive elastomer may be used. As a nonconductive elastomer, for example, silicone rubber, ethylene propylene rubber, ethylene propylene diene rubber, isoprene rubber, butadiene rubber, styrene butadiene rubber, nitrile rubber, chloroprene rubber, acrylonitrile nitrile butadiene rubber, butyl rubber, urethane rubber, or fluororubber Etc. These may be used alone or in combination of two or more. Among these, in terms of durability and the like, it is preferable to use silicone rubber. The base portion 20 and the terminal portion 30 are formed to include a nonconductive elastomer having rubber elasticity, and thus have a low elastic modulus. Therefore, at the time of use of the biological information measurement electrode according to the present embodiment, the base 20 and the terminal 30 are easily deformed into the uneven shape of the scalp and forehead, so that contact with the scalp and forehead can be ensured, The pressure on the forehead can be alleviated.

In the present embodiment, the base portion 20 and the terminal portion 30 are formed to include a carbon material, but may further include a conductive filler. Conductive fillers other than carbon materials include metals such as aluminum, gold, silver, copper, iron, platinum, chromium, tin, indium, antimony, titanium, or nickel; and so-called ABO ₃ type perovskite-type composite oxides Although conductive ceramics etc. are mentioned, it is not limited to these. These conductive fillers may be used alone or in combination of two or more.

<Manufacturing Method of Biological Information Measuring Electrode According to Second Embodiment>
Next, a method of manufacturing the biological information measuring electrode according to the second embodiment will be described. In the method of manufacturing the biological information measuring electrode according to the present embodiment, the base portion 20 and the terminal portion 30 are formed in the molding step S11 of the method of manufacturing the biological information measuring electrode according to the first embodiment shown in FIG. The material to be molded is changed, and a polishing process is provided between the molding process S11 and the surface treatment process S12.

FIG. 21 is a flowchart showing a method of manufacturing the biological information measuring electrode according to the present embodiment. An example of a state in which the raw material supply passage 61 used at the time of molding is fixed to the terminal portion 30 is shown in FIG.

In the method of manufacturing the biological information measuring electrode according to the present embodiment, as shown in FIG. 21, the base portion 20 and the terminal portion 30 are formed, and a plurality of tip grooves 24A are formed on the surface of the tip portion 221 which is the region A. Forming step (step S21) for forming the side groove portion 25 on the side surface 222, polishing step (step S22) for polishing the surface of the tip portion 221, and surface treatment step for activating the surface of the tip portion 221 Step S23) and a conductive layer forming step (Step S24) of forming a conductive layer 40 containing a conductive polymer on at least the surface of the tip end portion 221. Each step will be described below.

First, in the forming step (step S21), the material for forming the base portion 20 and the terminal portion 30 in the forming step S11 of the method for manufacturing the biological information measuring electrode according to the first embodiment shown in FIG. A resin material containing a carbon material is used. In the molding step (step S21), the base portion 20 and the terminal portion 30 are integrally molded using a resin material containing a carbon material, and a plurality of tip grooves 24A are formed on the surface of the tip portion 221. The side grooves 25 are formed.

The other contents such as the forming method of the base portion 20 and the terminal portion 30 are the same as the forming step S11 of the method of manufacturing the biological information measuring electrode according to the first embodiment shown in FIG. I omit it.

Next, in the polishing step (step S22), the surface of the tip portion 221 is polished. When molding the base portion 20 and the terminal portion 30 using a resin material containing a carbon material in the molding step (step S21), the proportion near the surface of the tip portion 221 does not contain the carbon material but contains the resin material There may be a high layer (skin layer). Since the skin layer does not contain a carbon material or the content thereof is very small even if it is contained, the conduction of the base portion 20 and the terminal portion 30 can not be achieved or the conduction becomes difficult. In the polishing step (step S22), the surface of the tip end portion 221 is polished to remove the skin layer present on the surface of the tip end portion 221, whereby the tip end portion 221 can be stably conductive.

Further, on the surfaces of the base portion 20 and the terminal portion 30 obtained in the forming step (step S21), there are places where a part of the carbon material protrudes. By polishing the surface of the tip portion 221, the carbon material protruding from the surface of the tip portion 221 is scraped off. Thereby, the surface of the tip end portion 221 can be made flat or the surface unevenness can be reduced. As a result, for example, when the surface of the tip portion 221 exposed by peeling off a part of the conductive layer 40 comes into contact with the living body, the carbon material protruding from the surface of the tip portion 221 suppresses damage to the surface of the living body be able to.

As a method of polishing the surface of the distal end portion 221, it is sufficient to remove the skin layer present on the surface of the distal end portion 221 and to remove the carbon material protruding from the surface of the distal end portion 221. A known method such as using a physical polishing method using

Next, in the surface treatment step (step S23), the surface of the tip portion 221 is applied using a method of irradiating vacuum ultraviolet light (excimer UV light) by excimer or a method of plasma processing in a mixed gas containing Ar and oxygen. Activate the The surface treatment step (step S23) is the same as the surface treatment step (step S12) of the method of manufacturing the biological information measuring electrode according to the first embodiment shown in FIG.

Finally, in the conductive layer forming step (step S24), the conductive layer 40 containing a conductive polymer is formed on the surface of the tip portion 221. The conductive layer forming step (step S24) includes a coating step (step S241) and a drying step (step S242). The conductive layer forming step (step S24) is the same as the conductive layer forming step (step S14) of the method of manufacturing the biological information measuring electrode according to the first embodiment shown in FIG. Do.

Thus, by forming the base portion 20 including the tip portion 221 and the terminal portion 30 by a resin material including a carbon material, the base portion 20 including the tip portion 221 and the terminal portion 30 are formed by a resin material including a carbon material The obtained biological information measuring electrode is obtained. Since the biological information measuring electrode can be made more lightweight and flexible, even when the biological information measuring electrode is attached to the head of the subject, it is possible to reduce the giving of a feeling of weight or the like. Thereby, it is possible to measure an electroencephalogram as biological information without giving a subject a certain sense of tension or the like. In the present embodiment, the biological information measuring electrode can be made, for example, 56% lighter than an electrode of the same size in which the base portion is formed of metal and the surface is gold-plated.

[Modification]
Although an example of the manufacturing method of the living body information measurement electrode concerning this embodiment was shown, it is not limited to this. Below, the modification in the manufacturing method of the electrode for biological information measurement concerning this embodiment is explained.

In the present embodiment, in the molding step (step S21), the base portion 20 and the terminal portion 30 are simultaneously formed using a mold provided with a protrusion corresponding to the tip groove portion 24A and the side surface groove portion 25. It is not limited. For example, after the base portion 20 and the terminal portion 30 are separately molded and integrated respectively, the tip groove 24A and the side groove 25 may be formed later.

In this case, as shown in FIG. 22, in the method of manufacturing the biological information measuring electrode according to the present embodiment, the forming step (step S21) is a preparing step (step S211) of preparing the base portion 20 and the terminal portion 30. A bonding step of bonding and integrating the base portion 20 and the terminal portion 30 (step S212), and a groove forming step of forming the plurality of tip grooves 24A and the side grooves 25 on the surface of the tip portion 221 (step S213) And consists of. Then, as in the present embodiment, the polishing process (step S22) for polishing the surface of the tip 221, the surface treatment process (step S23) for activating the surface of the tip 221, and the surface of the tip 221 And a conductive layer forming step (step S24) of forming a conductive layer 40 containing a conductive polymer.

In the binding step (step S212) of the above-described forming step (step S21), the base portion 20 and the terminal portion 30 are integrated using a binding member. A known binding member can be used as the binding member used for this binding. For example, synthetic resin such as epoxy resin or urethane resin, or synthetic resin having elasticity such as rubber can be used. Further, in the bonding step (step S212), before bonding the base portion 20 and the terminal portion 30, the surface of the base portion 20 to be bonded to the terminal portion 30 is polished in advance to form the surface of the surface. While removing the skin layer which exists near, it is preferable to shave off the carbon material which protrudes from the surface of the said surface. Thus, the conduction between the base portion 20 and the terminal portion 30 can be stably maintained, and the bonding force between the base portion 20 and the terminal portion 30 can be strengthened.

In the above-described groove forming step (step S213), a plurality of tip grooves 24A and side grooves 25 are formed on the surface of the tip portion 221 using a laser beam, a cutting jig, or the like. At this time, the skin layer on the surface of the tip groove 24A and the side groove 25 is removed since the width and the depth are reduced sufficiently. Therefore, the tip groove 24A and the side groove 25 and the conductive layer 40 can be stably maintained in conduction.

Further, in the present embodiment, although the polishing step (step S22) is included, the surface of the tip portion 221 is polished, for example, when there is no skin layer near the surface of the tip portion 221 or little effect of the skin layer occurs. It may be omitted if it is not necessary.

Third Embodiment
A biological information measurement electrode according to a third embodiment will be described. The biological information measuring electrode according to the present embodiment has the width W1 and the maximum depth H1 of the distal end groove 24A of the distal end 221 of the electrode leg 22 of the biological information measuring electrode 10 according to the first embodiment described above changed. The other components are the same as those of the biological information measuring electrode 10 according to the first embodiment described above, and therefore, in the present embodiment, only the tip groove 24A will be described. The configuration of the biological information measurement electrode according to the present embodiment will be described with reference to FIGS. 1 to 6 showing the biological information measurement electrode 10 according to the first embodiment.

[Base part and terminal part]
In the present embodiment, the width W1 of the tip groove portion 24A formed in the tip portion 221 of the base portion 20 is preferably 200 μm to 450 μm. If the width W1 of the distal end groove 24A is in the above range, the scalp can easily bite into the distal end groove 24A, and can easily follow the shape of the surface of the scalp. The width W1 of the tip groove portion 24A is more preferably 250 μm to 400 μm, and still more preferably 300 μm to 350 μm.

The maximum depth H1 of the tip groove 24A is preferably 100 μm to 250 μm. As described above, the width W1 of the distal end groove 24A is as wide as 200 μm to 450 μm, and the scalp is apt to bite. If the maximum depth H1 of the end groove 24A is in the above range, a sufficient depth can be secured even if the scalp bites into the end groove 24A. Further, even if the conductive layer 40 is formed at the tip end portion 221 of the electrode leg 22, the tip groove portion 24A can ensure a predetermined depth. Furthermore, the variation in time until the contact impedance drops to a predetermined value (for example, 300 kΩ) or less can be reduced by the position of the tip groove 24A. In the present embodiment, the maximum depth H1 of the tip groove 24A is more preferably more than 100 μm and not more than 230 μm, and still more preferably 150 μm to 210 μm.

When the tip portion 221 is brought into contact with the scalp, the biological information measuring electrode 10 according to the first embodiment described above has a high amount of moisture held in the scalp, such as when the scalp is wet, etc. The liquid held by the tip groove 24A may not flow to the surface of the scalp in contact with the tip 221. Also, when the pressing force of the tip 221 against the scalp is high, the scalp is soft, so the scalp blocks the tip groove 24A, and the liquid held in the tip groove 24A contacts the tip 221 on the surface of the scalp. It may not flow. However, in the biological information measurement electrode according to the present embodiment, the width W1 and the maximum depth H1 of the tip groove 24A on the surface of the tip portion 221 are within the predetermined range as described above. Thereby, since the scalp can easily bite into the tip groove 24A, the contact area between the surface of the tip 221 and the scalp can be increased. Therefore, the contact impedance between the scalp and the biological information measurement electrode 10 can be further lowered, and the electroencephalogram can be measured more stably.

In the biological information measurement electrode according to the present embodiment, the width W1 and the maximum depth H1 of the tip groove portion 24A on the surface of the tip portion 221 are within the predetermined range as described above, to thereby obtain the surface of the living body. Even if the tip end portion 221 is brought into contact with a plurality of times, a change in the contact area between the surface of the tip end portion 221 and the scalp can be suppressed. Therefore, when electroencephalograms are measured a plurality of times, even if the tip portion 221 of the biological information measurement electrode according to this embodiment is brought into contact with the surface of the scalp every measurement, variation in the measured values of the electroencephalograms obtained is suppressed. Can increase the reliability of the obtained electroencephalogram measurements.

As described above, the electrodes for measuring biological information according to each of the above embodiments maintain electrical connection with the scalp and can stably measure biological information (brain waves) obtained from the scalp. Besides, for example, it can be suitably used as an electrode for measuring biological information in which information of various living bodies such as pulse wave, electrocardiogram, myoelectricity, body fat, etc. is brought into contact with the skin and measured. In addition, although a living body includes a human body or a living body other than the human body, etc., the biological information measuring electrode according to each of the above embodiments can be particularly suitably used for the human body.

Hereinafter, although an Example and a comparative example are shown and an embodiment is more concretely described, an embodiment is not limited by these examples.

Example 1
Example 1-1
[Production of electrodes for measuring biological information]
The base portion and the terminal portion are integrally formed by injection molding using an insulating material (thermoplastic polyester elastomer, trade name: Hytrel (registered trademark), manufactured by Toray DuPont), and then a cross is formed at the tip of the base portion. The tip groove of the mold (groove width: 400 μm, height: 500 μm) was formed. Next, a solution containing a conductive polymer (PEDOT / PSS) was applied to the tip of the electrode leg to form a coated layer, and then the coated layer was dried and cured to form a conductive layer. Thus, an electrode for measuring biological information was produced.

(Example 1-2)
The same procedure as in Example 1-1 was followed, except that the shape of the tip groove formed at the tip of the electrode leg was changed to a mesh shape.

(Comparative Example 1-1)
The same procedure as in Example 1-1 was carried out except that no groove was formed at the tip of the electrode leg.

[Evaluation of contact with living body]
The contact of the biological information measuring electrode with the skin (forehead) was evaluated by the stability and responsiveness of the contact of the biological information measuring electrode with the skin (forehead). The evaluation of the stability and responsiveness of the contact of the electrode for measuring biological information with the skin (forehead) was performed by measuring the impedance.

First, in order to evaluate the stability of the contact, the tip of the electrode leg of the biological information measurement electrode was immersed in an electrolytic solution (0.1 M NaCl aqueous solution), and the impedance of the tip in the electrolytic solution was measured. The frequency of measurement was 0.5 Hz to 1000 Hz. The measurement results are shown in FIG. FIG. 23 shows the measurement results of Example 1-1 and Comparative Example 1-1, in which the horizontal axis is the measurement frequency (unit: Hz) and the vertical axis is the impedance (unit: Ω).

The lower the impedance at the tip, the higher the sensitivity with which an electrical signal obtained from a living body can be detected. This indicates that the measurement accuracy of the biological information measurement electrode is higher. Also, if the impedance is lower at the lower frequency side, stable and accurate measurement can be performed at the frequency (10 Hz to 30 Hz) generally used for measurement.

Next, in order to evaluate the responsiveness of the contact, the tip of the electrode leg of the biological information measurement electrode was immersed in the electrolyte (0.1 M NaCl aqueous solution) and pulled up, and the electrolyte was contained in the tip groove. Thereafter, the frequency was set to 0.5 Hz to 1000 Hz, and the impedance (contact impedance) was measured when the electrode leg was in contact with the forehead as a living body. And the time when the contact impedance becomes 300 kΩ or less was measured. The measurement results are shown in Table 1. When the contact impedance is 300 kΩ or less, for example, measurement of an electroencephalogram becomes possible. In addition, it indicates that if the time in which the contact impedance is low is quick, the response is good and it is easy to measure the biological information.

[Evaluation result of contact with living body]
As shown in FIG. 23, the biological information measurement electrode of Example 1-1 has a lower impedance value at all measured frequencies than the biological information measurement electrode of Comparative Example 1-1, and it is about 50%. It dropped to a degree. Therefore, the electrode for measuring biological information according to the present embodiment can detect an electrical signal obtained from a living body with high sensitivity, and can also perform measurement on the lower frequency side.

As shown in Table 1, the biological information measurement electrodes of Example 1-1 and Example 1-2 have a contact impedance of 300 kΩ or less as compared with the biological information measurement electrode of Comparative Example 1-1. Is more than four times faster. Therefore, the biological information measurement electrode of the present embodiment is easy to measure biological information.

Therefore, if at least a tip groove is formed at the tip of the electrode leg and a conductive layer is formed on the surface of the tip, the time taken for the contact impedance with the living body to fall below a predetermined value can be shortened. It was confirmed that the electroencephalogram can be stably measured because the impedance of the electrode for use is reduced.

Example 2
(Example 2-1)
[Production of electrodes for measuring biological information]
The base portion and the terminal portion are integrally formed by injection molding using a resin material (long fiber carbon fiber reinforced 6 nylon, trade name: Torayca (registered trademark), Toray Industries, Inc.) containing a carbon material, and then the base portion A cross-shaped tip groove was formed at the tip of the. Next, as in Example 1-1 above, a solution containing a conductive polymer (PEDOT / PSS) is applied to the tip of the electrode leg to form a coated layer, and then the coated layer is dried and cured. To form a conductive layer. Thus, an electrode for measuring biological information was produced. The produced electrode for measuring biological information was 1.5 g.

(Example 2-2)
The same procedure as in Example 2-1 was followed except that the shape of the tip groove formed at the tip of the electrode leg was changed to a mesh shape.

(Comparative example 2-1)
The same procedure as in Example 2-1 was performed except that no groove was formed at the tip of the electrode leg.

(Comparative Example 2-2)
The same procedure as in Example 2-1 was performed except that the groove and the conductive layer were not formed at the tip of the electrode leg.

[Evaluation of contact with living body]
The contactability of the biological information measurement electrode with the skin (forehead) was evaluated based on the stability and responsiveness of the contact of the biological information measurement electrode with the skin (forehead), as in Example 1. The evaluation of the stability and responsiveness of the contact of the electrode for measuring biological information with the skin (forehead) was performed by measuring the impedance.

First, as evaluation of the stability of the contact, the tip of the electrode leg of the electrode for measuring biological information is immersed in the electrolyte (0.1 M aqueous solution of NaCl) as in Example 1-1 above to make the electrolyte The impedance of the tip in the inside was measured. The frequency of measurement was 0.5 Hz to 1000 Hz. The measurement results are shown in FIG. FIG. 24 shows the measurement results of Example 2-1 and Comparative Example 2-1 in which the horizontal axis is the measurement frequency (Hz) and the vertical axis is the impedance (Ω).

Next, as an evaluation of the stability of the similar contact, the impedance of the tip in “before electroencephalogram measurement (initial) / after electroencephalogram measurement / after alcohol washing” was measured. In the measurement method, the impedance in the electrolyte (0.1 M NaCl aqueous solution) was measured in the same manner as described above, and the measured frequency was 1 Hz to 1000 Hz. The measurement results are shown in FIG. 25 and FIG. FIG. 25 shows the measurement result of impedance when using the biological information measurement electrode of Example 2-1, and FIG. 26 shows the measurement result of impedance when using the biological information measurement electrode of Comparative Example 2-2 Are shown respectively. In FIG. 25 and FIG. 26, the broken line indicates the measurement value before electroencephalogram measurement, the alternate long and short dash line indicates the measurement value after electroencephalogram measurement, and the solid line indicates the measurement value after alcohol washing of the tip. .

Next, the responsiveness of the contact was evaluated in the same manner as in Example 1-1 above. That is, in order to evaluate the responsiveness of the contact, the tip of the electrode leg of the biological information measurement electrode was immersed in the electrolyte (0.1 M NaCl aqueous solution) and pulled up, and the electrolyte was contained in the tip groove. Thereafter, the frequency was set to 0.5 Hz to 1000 Hz, and the impedance (contact impedance) was measured when the electrode leg was in contact with the forehead as a living body. And the time when the contact impedance becomes 300 kΩ or less was measured. The measurement results are shown in Table 2. When the contact impedance is 300 kΩ or less, for example, measurement of an electroencephalogram becomes possible.

[Evaluation result of contact with living body]
The lower the impedance at the tip, the higher the sensitivity with which an electrical signal obtained from a living body can be detected. This indicates that the measurement accuracy of the biological information measurement electrode is higher. Also, if the impedance is lower at the lower frequency side, stable and accurate measurement can be performed at the frequency (10 Hz to 30 Hz) generally used for measurement. In addition, it indicates that if the time in which the contact impedance is low is quick, the response is good and it is easy to measure the biological information.

As shown in FIG. 24, the biological information measuring electrode of Example 2-1 having a tip groove and a conductive layer at the tip of the electrode leg was measured more than the biological information measuring electrode of Comparative Example 2-1. Low impedance values were obtained at all frequencies, down to about 50%. Therefore, the electrode for measuring biological information according to the present embodiment can detect an electrical signal obtained from a living body with high sensitivity, and can also perform measurement on the lower frequency side.

As shown in FIGS. 25 and 26, in the electrode for measuring biological information of Example 2-1, no change was observed in the impedance before and after the measurement of the electroencephalogram, and the same impedance was obtained even after the alcohol washing. On the other hand, in the electrode for measuring biological information of Comparative Example 2-2, the impedance was significantly increased after electroencephalogram measurement and decreased after washing with alcohol, but did not return to the value before electroencephalogram measurement. Therefore, the electrode for measuring biological information according to the present embodiment can stably detect an electrical signal obtained from a living body, and can be said to be resistant to cleaning (wipe) and the like.

As shown in Table 2, the biological information measuring electrodes of Example 2-1 and Example 2-2 have a contact impedance of 300 kΩ or less, as compared with the biological information measuring electrode of Comparative Example 2-1. Is more than 1.8 times faster. Therefore, the biological information measurement electrode of the present embodiment is easy to measure biological information.

Example 3
Example 3-1
[Production of electrodes for measuring biological information]
The base portion and the terminal portion are integrally formed by injection molding using an insulating material (thermoplastic polyester elastomer, trade name: Hytrel (registered trademark), manufactured by Toray Dupont), and then the tip portion of the base portion is Six tip grooves as shown in FIG. 12 (groove width: 350 μm, maximum depth:
150 μm) were formed radially at substantially the same angle (about 60 °) in plan view of the tip. Then, a solution containing a conductive polymer (PEDOT / PSS) (a solution containing a polythiophene-based conductive polymer (Sepluzida OC-AE 401 G, Shin-Etsu Polymer Co., Ltd.)) is applied to the tip of the electrode leg. After forming the coating layer, the coating layer was dried and cured to form a conductive layer. Thus, an electrode for measuring biological information was produced.

Example 3-2
The procedure was carried out in the same manner as in Example 3-1 except that the tip groove portion formed at the tip portion of the electrode leg was changed to a radial arrangement of eight pieces at substantially the same angle (about 45 °) in plan view of the tip portion. .

(Example 3-3)
The same procedure as in Example 3-1 was carried out except that the shape of the tip groove formed at the tip of the electrode leg was changed to providing a stitch in a plan view of the tip as shown in FIG.

Example 3-4
The same procedure as in Example 3-1 is carried out except that, as shown in FIG. 15, the recessed portion (hole diameter: 350 μm, maximum depth: 150 μm) is changed to the tip end portion of the electrode leg instead of the end groove portion. I went.

(Examples 3-5 to 3-7)
The same procedure as in Examples 3-1 to 3-3 was performed, except that the groove width of the tip groove formed at the tip of the electrode leg in Examples 3-1 to 3-3 was changed to 450 μm.

(Example 3-8)
The same procedure as in Example 3-4 was performed, except that the groove width of the depressed portion formed at the tip of the electrode leg of Example 3-4 was changed to 450 μm.

(Comparative Example 3-1)
Example 3-1 was carried out in the same manner as Example 3-1 except that the biological information measuring electrode manufactured in Comparative Example 1-1 described above was used.

[Evaluation of responsiveness of contact with living body]
The evaluation of the responsiveness of the contact of the electrode for measuring biological information with the skin (the forehead) was performed by measuring the contact impedance.

As evaluation of the responsiveness of the contact, the electrode leg of the electrode for measuring biological information was brought into contact with the forehead. Thereafter, the frequency was set to 0.5 Hz to 1000 Hz, and the impedance (contact impedance) when the electrode leg was in contact with the forehead as a living body was measured using an electroencephalograph (Polymate Mini AP108, Miyuki Giken Co., Ltd.). And the time when the contact impedance becomes 300 kΩ or less was measured. Thereafter, the electrode leg was separated from the living body and the tip was washed. The measurement of the time when the contact impedance was 300 kΩ or less was repeated five times in Examples 3-1 to 3-4 and Comparative Example 3-1. Table 3 and FIG. 27 show measurement results of the time until the contact impedance of the electrodes for measuring biological information of Examples 3-1 to 3-4 and Comparative Example 3-1 falls to 300 kΩ or less and the absolute value of the error. Shown in. The error of time until contact impedance falls to 300 kΩ or less is the difference between the maximum value and the minimum value of the time until contact impedance falls to 300 kΩ or less according to the following equation (1) (maximum value-minimum value) Do. When the contact impedance is 300 kΩ or less, for example, measurement of an electroencephalogram becomes possible. In addition, it indicates that if the time in which the contact impedance is low is quick, the response is good and it is easy to measure the biological information.

[Evaluation result of stability of contact with living body]
As shown in FIG. 27, the biological information measurement electrodes of Examples 3-1 to 3-8 have shorter contact impedance times of 300 kΩ or less than the biological information measurement electrodes of Comparative Example 3-1. Both became less than 300 kΩ in 10 seconds or less. The biological information measuring electrodes of Examples 3-1 to 3-8 had smaller variations in contact impedance than the biological information measuring electrodes of Comparative Example 3-1. Therefore, the biological information measuring electrode in which the tip groove portion or the recess portion of a predetermined size is formed at the tip end portion of the electrode leg can stably perform the measurement of biological information.

In addition, in each Example and the comparative example, when the electrode for biological information measurement was used repeatedly, the tendency until a contact impedance became 300 k (ohm) or less tends to produce dispersion easily. This is considered to be due to the fact that the position at which the tip portion contacts the forehead is slightly shifted for each measurement when repeatedly using the biological information measuring electrode. Moreover, it is thought that the contamination condition etc. of a front-end | tip part differ by having used the electrode for a biometric information measurement repeatedly and contacting a front-end | tip part to a forehead.

As described above, when a tip groove or recess having a predetermined groove width and maximum depth is formed at the tip of the electrode leg and a conductive layer is formed on the surface of the tip, the contact impedance with the living body is less than a predetermined value. It was confirmed that the brain waves can be measured stably because the time to become to become faster and the variation becomes smaller.

Example 4
Example 4-1
[Production of electrodes for measuring biological information]
The base portion and the terminal portion are integrally formed by injection molding using an insulating material (thermoplastic polyester elastomer, trade name: Hytrel (registered trademark), manufactured by Toray Dupont), and then the tip portion of the base portion is The two tip grooves (groove width: 350 μm, maximum depth: 150 μm) were formed in a straight line so as to face each other at substantially the same angle (about 180 °) in plan view of the tip. Then, a solution containing a conductive polymer (PEDOT / PSS) (a solution containing a polythiophene-based conductive polymer (Sepluzida OC-AE 401 G, Shin-Etsu Polymer Co., Ltd.)) is applied to the tip of the electrode leg. After forming the coating layer, the coating layer was dried and cured to form a conductive layer. Thus, an electrode for measuring biological information was produced.

(Example 4-2)
Example 4--except that the tip groove portion formed at the tip portion of the electrode leg is provided four at substantially the same angle (90 °) in plan view of the tip portion to form the tip groove portion shown in FIG. It went in the same way as 1.

Example 4-3
Example 4--except that the tip groove portion formed at the tip portion of the electrode leg is provided six at substantially the same angle (60 °) in a plan view of the tip portion to form the tip groove portion shown in FIG. It went in the same way as 1.

(Example 4-4)
Example 4 was carried out in the same manner as Example 4-1 except that eight tip grooves formed at the tip of the electrode leg were provided at substantially the same angle (45 °) in plan view of the tip.

(Example 4-5)
The same procedure as in Example 4-1 was carried out except that the shape of the tip groove formed at the tip of the electrode leg was changed to a stitch shape in a plan view of the tip.

(Example 4-6)
Similar to Example 4-1 except that instead of the end groove portion, a recessed portion (hole diameter: 350 μm, maximum depth: 150 μm) is formed at the end portion of the electrode leg as shown in FIG. I went.

(Examples 4-7 to 4-11)
The same procedure as in Examples 4-1 to 4-5 was performed, except that the maximum depth of the tip groove formed at the tip of the electrode leg in Examples 4-1 to 4-5 was changed to 250 μm. .

Example 4-12
Example 4-6 was carried out in the same manner as Example 4-6, except that the maximum depth of the depression formed at the tip of the electrode leg of Example 4-6 was changed to 250 μm.

(Comparative Example 4-1)
The same procedure as in Example 4-1 was repeated except that the biological information measuring electrode manufactured in Comparative Example 1-1 described above was used.

As evaluation of the responsiveness of the contact, the electrode leg of the electrode for measuring biological information was brought into contact with the forehead. Thereafter, the frequency was set to 0.5 Hz to 1000 Hz, and the impedance (contact impedance) when the electrode leg was in contact with the forehead as a living body was measured using an electroencephalograph (Polymate Mini AP108, Miyuki Giken Co., Ltd.). And the time when the contact impedance becomes 300 kΩ or less was measured. Thereafter, the electrode leg was separated from the living body. The measurement of the time when the contact impedance became 300 kΩ or less was repeated five times in Examples 4-1 to 4-12 and Comparative Example 4-1. The measurement results of the time until the contact impedance of the electrodes for measuring biological information of each Example and Comparative Example falls to 300 kΩ or less and the absolute value of the error are shown in FIG. The error in the time until the contact impedance falls to 300 kΩ or less is the difference between the maximum value and the minimum value of the time until the contact impedance falls to 300 kΩ or less (maximum value-minimum value) as in the above-mentioned Example 3. I assume. When the contact impedance is 300 kΩ or less, for example, measurement of an electroencephalogram becomes possible. In addition, it indicates that if the time in which the contact impedance is low is quick, the response is good and it is easy to measure the biological information.

[Evaluation result of stability of contact with living body]
As shown in FIG. 28, the biological information measurement electrodes of Examples 4-1 to 4-12 have shorter contact impedance times of 300 kΩ or less than the biological information measurement electrodes of Comparative Example 4-1. Both became less than 300 kΩ in 21 seconds or less. Further, the electrodes for measuring biological information of Examples 4-1 to 4-12 had smaller variations in contact impedance than the electrodes for measuring biological information of Comparative Example 4-1. Therefore, the biological information measuring electrode in which the tip groove or depression of a predetermined size is formed at the tip of the electrode leg can stably measure biological information.

In addition, in each Example and the comparative example, when the electrode for biological information measurement was used repeatedly, the tendency until a contact impedance became 300 k (ohm) or less tends to produce dispersion easily. This is considered to be due to the fact that the position at which the tip portion contacts the forehead is slightly deviated for each measurement when repeatedly using the biological information measurement electrode as described in the third embodiment. Moreover, it is thought that the contamination condition etc. of a front-end | tip part differ by having used the electrode for a biometric information measurement repeatedly and contacting a front-end | tip part to a forehead.

Therefore, if a tip groove or depression having a predetermined maximum depth or more is formed at the tip of the electrode leg and a conductive layer is formed on the surface of the tip, the contact impedance with the living body is reduced to a predetermined value or less. It has been confirmed that the brain waves can be measured stably because the variation becomes smaller as the time becomes faster.

Example 5
(Examples 5-1 and 5-2 and Comparative Example 5-1)
[Production of electrodes for measuring biological information]
In Examples 5-1 and 5-2 and Comparative Example 5-1, the electrodes for measuring biological information prepared in Examples 3-2 and 3-3 and Comparative Example 1-1 described above were used, respectively.

[Evaluation of contact with living body]
The contact of the biological information measuring electrode with the living body was evaluated by measuring the contact resistance (resistance value) when the tip of the biological information measuring electrode was brought into contact with a soft surface.

The contact resistance is evaluated by applying a load of 50 g to the surface of a conductive silicone sponge (Si-500, hardness E20) with the tip of the electrode leg of the electrode for measuring biological information as a soft surface, 6241A (manufactured by AGC Co., Ltd.) to measure the resistance value. The measurement results of the resistance when using the electrodes for measuring biological information of Examples 5-1 and 5-2 and Comparative Example 5-1 are shown in FIG.

[Evaluation result of contact with living body]
As shown in FIG. 29, the electrodes for measuring biological information of Examples 5-1 and 5-2 had a resistance value reduced to 1⁄5 or less that of the electrode for measuring biological information of Comparative Example 5-1. Therefore, the biological information measuring electrode in which the tip groove is formed at the tip of the electrode leg is likely to bite the surface of the living body, so the time until the contact impedance becomes 300 kΩ or less is accelerated, and the electric signal obtained from the living body is high. It enables stable detection with sensitivity.

As mentioned above, although embodiment was described, said each embodiment is shown as an example, and this invention is not limited by the said embodiment. The above embodiments can be implemented in other various forms, and various combinations, omissions, replacements, changes, and the like can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and the gist of the invention, and are included in the invention described in the claims and the equivalent scope thereof.

The present application is based on Japanese Patent Application No. 2017-252506 filed Dec. 27, 2017, and Japanese Patent Application No. 2017-252507 filed Dec. 27, 2017. The entire contents of Japanese Patent Application No. 2017-252506 and Japanese Patent Application No. 2017-252507 are incorporated in the present application.

DESCRIPTION OF REFERENCE NUMERALS 10 electrode for biological information measurement 20

base portion

21, 301 base portion 211 protruding portion 22 electrode leg 221 tip portion 222

side surface

24 A, 24 B, 24 C groove portion (tip groove portion)
25 Auxiliary groove (side groove)
30 terminal portion 40 conductive layer A region H1, H2 maximum depth W1, W2 width

Claims

An electrode for measuring biological information, having a region accessible to a living body,
A plurality of grooves or depressions are formed on the surface of the region, and a conductive layer containing a conductive polymer is also formed.
A plurality of auxiliary grooves are formed on the surface of the portion other than the region,
The biological information measuring electrode according to claim 1, wherein the auxiliary groove communicates with at least a part of the groove.
The width of the groove is 10 to 450 μm,
The biological information measuring electrode according to claim 1 or 2, wherein the maximum depth of the groove is 10 to 500 μm.
The biological information measuring electrode according to claim 3, wherein the width of the groove is 10 to 120 μm.
The width of the groove is 200 to 450 μm,
The biological information measuring electrode according to claim 3, wherein the maximum depth of the groove is 100 to 250 μm.
The biological information measuring electrode according to any one of claims 1 to 5, wherein the grooves are provided radially, reticulated, or dendritic on the surface of the region.
The width of the recess is 10 to 450 μm,
The biological information measuring electrode according to claim 1, wherein the maximum depth of the recess is 10 to 500 μm.
The biological information measuring electrode according to any one of claims 1 to 7, wherein the region is formed of a resin material containing a carbon material.
A base portion provided with the area;
A terminal portion electrically connected to the region;
The biological information measuring electrode according to any one of claims 1 to 8, comprising:
A method of manufacturing a biological information measuring electrode having a region accessible to a living body, the method comprising:
Forming a base having the region, and forming a plurality of grooves on the surface of the region;
A conductive layer forming step of forming a conductive layer containing a conductive polymer on at least the surface of the region;
A method of manufacturing a biological information measuring electrode comprising:
The method according to claim 10, wherein in the forming step, the base portion is formed of a resin material containing at least a carbon material.
The biological information according to claim 11, further comprising a polishing step of polishing the surface of at least the region of the substrate portion after forming the substrate portion, and removing the carbon material protruding from the surface of the region at least. Method of manufacturing measurement electrode.
The method further includes a surface treatment step of activating the surface of at least the region after forming the plurality of grooves on the surface of the region,
The surface treatment step is a step of plasma treating at least the surface of the region in a mixed gas containing Ar and oxygen, or irradiating at least the surface of the region with excimer UV light. The manufacturing method of the electrode for biometric information measurement as described in any one.
The conductive layer forming step
Applying a solution containing the conductive polymer to at least the region to form a coating layer;
Drying the area in which the coating layer is formed to cure the coating layer;
The manufacturing method of the electrode for biometric information measurement as described in any one of Claims 10 thru | or 13 containing these.