JP6808897B2 - Biological signal detection orthosis and biological signal detection method - Google Patents

Description

The present invention relates to a technique for detecting a biological signal from an electrode attached to a living body including a human body and attached to the surface of the living body, and in particular, the biological signal of the first part and a second part having a different position from the first part. Biological signal detection that can easily adjust the biological signal of a part even when the distance from the first part to the second part differs due to individual differences in the living body, and can detect the biological signal with high accuracy. Regarding equipment and biological signal detection method.

In recent years, there has been increasing public interest in maintaining or improving health. Therefore, for health management, people can more easily in their daily lives, for example, heartbeat signals, electrocardiographic signals, brain wave signals (electrical (potential) signals generated by brain activity), and myoelectric signals (moving muscles). It is desired to detect biological information such as electric (potential) signals that occur occasionally) with high accuracy. Further, it is desired to detect the above-mentioned biological information with high accuracy not only in health management but also in diagnosis and treatment of diseases, and further, not only in the human body but also in animal experiments and the like, the above-mentioned biological information is accurately detected. It is desired to detect it highly.

For example, an electrocardiographic signal detection device that easily detects biological information with high accuracy in daily life is disclosed in Japanese Patent No. 5843005 (Patent Document 1). This electrocardiographic signal detection device is electrically connected to each other and is attached to the left and right outer ears in contact with the first and second outer ear electrodes, and the upper arm / shoulder electrode is attached in contact with the upper arm or shoulder. An electrocardiographic signal connected to the first outer ear electrode, the second outer ear electrode, and the upper arm / shoulder electrode, and detected by the first outer ear electrode, the second outer ear electrode, and the upper arm / shoulder electrode. It is characterized by being provided with a measuring means for measuring. According to this electrocardiographic signal detection device, the user can measure the electrocardiographic signal while performing daily movements / activities (for example, exercise).

Further, Patent Document 1 discloses that it is preferable that the outer ear electrode is attached in contact with a portion including a boundary region between the auricle and the earlobe constituting the outer ear. Further, in the embodiment of Patent Document 1, in order to detect an electrocardiographic signal, a combination of an external ear electrode and an upper arm electrode (first, second and third embodiments) and a combination of a forehead electrode and an upper arm electrode (first). 4 embodiments) and a combination of two left and right brachial electrodes (fifth embodiment) are disclosed.

Japanese Patent No. 5843005

According to the electrocardiographic signal measuring device disclosed in Patent Document 1, since the electrocardiographic electrodes (external ear electrode / forehead electrode and upper arm electrode) are attached to the outer ear / forehead and the upper arm, it is necessary to take off clothes when attaching / detaching the electrocardiographic electrode. There is no need to put on and take off, and the electrocardiographic electrodes are attached to the outer ear / forehead and upper arm, so both hands are not blocked and the electrocardiographic signal is performed while performing other movements (for example, exercise). Can be measured.

However, in the electrocardiographic signal measuring device disclosed in Patent Document 1, at least two parts of the human body (two parts of the external ear electrode and the upper arm electrode, two parts of the left and right upper arm electrodes, or two parts of the forehead electrode and the upper arm) whose positions are significantly different are used. Since the electrocardiographic electrode must be attached to (two parts with the electrode), it does not take time to attach and detach as described above, but it takes a considerable amount of time to adjust the position. In particular, since the detection accuracy of a bioelectrode including an electrocardiographic electrode attached to a living body varies greatly depending on the attachment position, it takes a considerable amount of time and effort to adjust the position. Further, since the preferable mounting position of the bioelectrode differs depending on the individual difference (difference in physique) of the living body, it takes a considerable amount of time and effort to adjust the position.

The present invention has been developed in view of the above-mentioned problems of the prior art, and an object of the present invention is a living body that is attached to a living body including a human body and detects a biological signal from an electrode attached to the surface of the living body. The distance from the first part to the second part of the signal detection device, which is the biological signal of the first part and the biological signal of the second part whose position is different from that of the first part, due to individual differences of the living body. It is an object of the present invention to provide a biological signal detection device and a biological signal detection method that can be easily adjusted and can detect a biological signal with high accuracy even if they are different.

In order to achieve the above object, the biological signal detection orthosis according to the present invention takes the following technical measures.
That is, the biological signal detection device according to a certain aspect of the present invention is attached to a living body and detects a biological signal of a first part in the living body and a biological signal of a second part whose position is different from that of the first part. A first of the biological signal detection devices to be provided, which is provided at a position corresponding to the first portion of the ring and the annular base material layer having at least a part of elasticity. A first detecting means for detecting the biological signal of the above, and a second detecting means provided at a position corresponding to the second portion in the ring and detecting the second biological signal for the second portion. , An expansion and contraction that is electrically connected to the first detecting means and the second detecting means, and electrically flows a signal detected by the first detecting means and a signal detected by the second detecting means. The conductive harness is joined to the base material layer, including a conductive harness having a property.

Preferably, the conductive harness has a conductive portion knitted by mixing a conductive thread and an elastic thread and a non-conductive portion knitted only by the non-conductive thread, and the conductive portion has the conductive portion. Two or more electrically independent constituent paths using a metal wire as a thread are provided, and each of the detection means differs between the first portion and the second portion from the two or more constituent paths. It can be configured to include a bioelectrode selected and electrically connected.

More preferably, the conductive harness has a conductive portion knitted by mixing a conductive thread and an elastic thread and a non-conductive portion knitted only by the non-conductive thread, and the conductive portion has the above-mentioned conductive portion. Two or more electrically independent constituent paths using a metal wire as the conductive thread are provided, and each of the detection means includes a first portion and a second portion from the two or more constituent paths. It can be configured to include a terminal selected differently and electrically connected and attached to the conductive harness and a bioelectrode electrically connected to the terminal.

More preferably, at least one of the first detecting means and the second detecting means is described in order to adjust that the distance from the first part to the second part differs depending on the individual difference of the living body. A plurality of terminals attached to the conductive harness can be provided, and the bioelectrode can be configured to be electrically connected to any of the plurality of terminals.
More preferably, the terminal comprises either one of a pair of metal snap buttons on the male and female sides, and the bioelectrode comprises an electrode layer made of a fiber knitted fabric. The surface roughness (Ra) of the knitted fabric is 40 μm or less, and the fiber knitted fabric can be configured to be provided with a snap button on the other side paired with the one side.

More preferably, the fiber knitted fabric is provided with a snap button on the other side paired with the one side, and is provided with a hole corresponding to the size of the male portion, and the male side is provided with a hole portion through the hole portion. The snap button and the snap button on the female side can be fitted so that the bioelectrode can be attached to the terminal.
More preferably, the biological signal detection device is attached to the head of the human body to detect the biological signal on the forehead as the first biological signal and detect the biological signal at the base of the auricle as the second biological signal. A plurality of terminals constituting the second detecting means for detecting the biological signal at the base of the auricle are provided in the conductive harness, and in the second detecting means, the bioelectrode is the second. It can be configured to be electrically connected to any one of the plurality of terminals constituting the detection means that matches the position of the base of the pinna.

Further, the biological signal detection method according to another aspect of the present invention is attached to the head of a human body and detects a biological signal on the forehead as a first part and a biological signal at the base of the auricle as a second part. This is a biological signal detection method using a biological signal detection device. The biometric signal detection device used in this biometric signal detection method is provided at a position of an annular base material layer having at least a part of elasticity and a base material layer corresponding to the first portion, and is provided at the position of the first base material layer. The first detecting means for detecting the first biometric signal for the site and the second biometric signal for the second site provided at the position of the base material layer corresponding to the second site. A second detecting means, a harness having elasticity through which a signal detected by the first detecting means and a signal detected by the second detecting means electrically flow, and the base material layer. The conductive harness includes a conductive harness joined to the above, and the conductive harness has a conductive portion knitted by mixing a conductive thread and an elastic thread and a non-conductive portion knitted only by a non-conductive thread. , The conductive portion is provided with two or more electrically independent constituent paths that employ a metal wire as the conductive thread, and each of the detecting means is a first portion from the two or more constituent paths. The second detection includes a terminal that is selected and electrically connected to the conductive harness so as to be different between the second portion and the second portion, and a bioelectrode electrically connected to the terminal. The means comprises a plurality of terminals attached to the conductive harness, and the bioelectrode is electrically connected to any of the plurality of terminals. The biological signal detection method using this biological signal detection device has an expansion step of artificially expanding the annular diameter of the base material layer and the conductive harness bonded to the base material layer, and an annular diameter. After fitting the expanded biological signal detection device on the head of the human body, the attachment step of canceling the artificial expansion and attaching the biological signal detection device to the head of the human body, and the first detection means The first part determination step of adjusting the position to the position of the forehead of the human body and one of the plurality of terminals constituting the second detection means that matches the position of the base of the ear canal are selected. A selection step to be performed, a connection step of electrically connecting a biological electrode to the selected terminal, and a detection for detecting a biological signal in the forehead, which is the first site, and a biological signal in the external ear, which is the second site. Including steps.

According to the biological signal detection device and the biological signal detection method according to the present invention, in the biological signal detection device which is attached to a living body including a human body and detects a biological signal from an electrode attached to the surface of the biological body, the biological signal of the first portion And the biological signal of the second part, which is different from the first part, can be easily adjusted even when the distance from the first part to the second part is different due to individual differences of the living body. , It becomes possible to detect biological signals with high accuracy.

It is a figure which attached the headband for measuring the biological signal which is an example of the biological signal detection device which concerns on this invention to the head of a human body. It is an overall perspective view of the headband for measuring a biological signal of FIG. It is an exploded view of the headband for measuring a biological signal of FIG. (A) is a plan view of the conductive harness constituting the head band for measuring biological signals in FIG. 1, and (B) is a non-extended state in a double-sided stitch view in the cross-sectional direction in which the conductive portion of the conductive harness is smoothly formed. The figure shown, (C) is a figure showing the extended state, and (D) is a schematic cross-sectional view of the biological electrode constituting the head band for measuring the biological signal of FIG. It is a top view of the take-out board attached to the conductive harness of FIG. 4A. It is a figure for demonstrating the procedure of attaching a bioelectrode to the take-out substrate of FIG. It is an exploded view of the headband for measuring a biological signal which is a modification of the biological signal detection device which concerns on this invention. FIG. 7 is a diagram in which the headband for measuring biological signals of FIG. 7 is attached to the head of a human body.

Hereinafter, embodiments of the present invention will be described with reference to the drawings. In the present embodiment, a headband for measuring a biological signal (which may be simply referred to as a headband below), which is an example of the biological signal detection orthosis according to the present invention, is worn on the head of a human body. Equipment and methods for detecting signals (mainly brain waves) will be described, but the present invention is not limited thereto. Therefore, the present invention targets a living body (experimental animal, etc.) not limited to the human body, and is attached to a part of the living body (upper arm, lower limb, etc.) not limited to being worn on the head, and is not limited to an electroencephalogram. It includes a biological signal detection device for detecting a heartbeat signal, an electrocardiographic signal, a myoelectric signal, etc.) and a biological signal detection method. Further, in the description using the drawings, the description may be made using the vertical and horizontal directions, but the biological signal detection device according to the present invention is not limited to such a direction. Here, the left-right direction is the left-right direction seen from the subject wearing the headband 100 on the head.

First, with reference to FIGS. 1 to 3, the schematic structure of the headband 100 according to the present embodiment will be described, and then the detailed structure of each part and the biological signal detection method using the headband 100 will be described.
<Outline structure of headband>
1A and 1B are views in which the headband 100 is attached to the head H of a human body as a subject, FIG. 1A is a perspective view from the front, FIG. 1B is a perspective view from the rear, and FIG. C) is a plan view from the side. FIG. 2 is an overall perspective view of the headband 100 alone (not worn on the subject's head H), FIG. 2 (A) is a perspective view from the front, and FIG. 2 (B) is a rear view. It is a perspective view of. FIG. 3 is an exploded top view of the headband 100.

As shown in these figures, the headband 100 is attached to a living body (here, a human body) and has a biological signal of a first part S (B) and a position of the first part S (B) in the living body. The biological signal of a different second site S (C) is detected. The headband 100 is provided at a position corresponding to the annular base material layer 110 having at least a part of elasticity and the first portion S (B) in the annular shape, and is provided with respect to the first portion S (B). The first detection means 220B for detecting the first biological signal and the second biological signal for the second portion S (C) provided at the position corresponding to the second portion S (C) in the ring. The second detecting means 220C to be detected is electrically connected to the first detecting means 220B and the second detecting means 220C, and is detected by the signal detected by the first detecting means 220B and the second detecting means 220C. The conductive harness 200 is joined to the annular base material layer 110, including the elastic harness 200 through which the signal is electrically flowed.

The first biological signal and the second biological signal are biopotential signals (here, brain wave potential signals), and the first biological signal for the first part S (B) is the left and right first parts. It is a potential difference between S (B), and the second biological signal for the second part S (C) is a potential difference between the left and right second parts S (C) (for details, these potential differences are described respectively. Amplified signal). Here, the reference detection means 220A is provided at a position corresponding to the substantially central portion (not shown, but referred to as the reference portion S (A)), and the biological signal (reference biological signal) detected by the reference detection means 220A is It is used as a reference potential during measurement. Then, in addition to the first biological signal and the second biological signal, the reference biological signal electrically flows through the conductive harness 200. Here, since the basic structures of the reference detecting means 220A, the first detecting means 220B, and the second detecting means 220C are the same, they may be collectively described as the detecting means 220. The detection signal detected by these a plurality of detection means is taken out from the take-out board 240 provided on the back of the head to the outside of the headband 100 via the lead wire 240, and is amplified by an amplifier or the like (analog amplification processing).

As will be described in detail later, in this headband 100, a 4-wire type is adopted as the conductive harness 200 (1 wire is a spare), and the detection circuits are made independent on the left and right sides of the head (the part of the terminal board board 222A). And at the end 202 of the conductive harness 200), the electroencephalogram signals (reference signals are common to the left and right) are detected at three locations on each side. Further, the second site S (C) is a point (point in the region S) where the second biological signal (electroencephalogram signal) can be detected with the highest accuracy in the region S corresponding to the base of the pinna Y. ).

The detailed structure of each part of the headband 100 will be described in detail below.
<Detailed structure of headband>
-Conductive harness First, the conductive harness 200 through which a detection signal flows will be described. FIG. 4A is a plan view of the conductive harness 200, and FIG. 4B is a diagram showing a non-extended state in a double-sided stitch diagram in the cross-sectional direction in which the conductive portion 1 of the conductive harness 200 is smoothly formed. , A diagram showing the extended state is shown in FIG. 4 (C), respectively. The conductive harness 2 shown in FIG. 4 and the conductive harness 200 shown in another figure are the same.

The conductive harness 2 has a conductive portion 1 knitted by mixing a conductive thread 10 and an elastic thread 11 and a non-conductive portion 3 (4) knitted only by a non-conductive thread, and is a conductive portion. In No. 1, at least the conductive threads 10 are provided in a zigzag shape in the front and back directions in the knitted fabric, and the elastic threads 11 generate a tightening force along the front and back surface directions of the knitted fabric to generate a tightening force of the conductive threads 10. The conductive portion 1 is provided with a configuration path in which a metal wire is used as the conductive yarn 10, and the non-conductive portion 3 (4) is provided with synthetic fibers as the non-conductive yarn. It is characterized in that the adopted configuration route is provided.

As shown in FIG. 4A, it is a plan view showing the conductive harness 2 (hereinafter, may be simply referred to as “harness 2”). The harness 2 is formed in the shape of a flat and elongated band, and is provided with two conductive portions 1 and 1 parallel to each other in the longitudinal direction of the band. Further, FIGS. 4 (B) and 4 (C) are double-sided stitch views showing the knitted fabrics constituting the conductive portions 1 and 1.

In the example shown in FIG. 4A, the conductive portion 1 is formed in a strip shape and is exposed on the front and back surfaces of the harness 2, and the two conductive portions 1 and 1 are short-circuited with each other. It is assumed that the non-conductive portion 3 for prevention is provided.
Further, a non-conductive portion 4 is also provided outside in the band width direction with respect to the conductive portions 1 and 1, and when the side edge portion of the harness 2 comes into contact with another object, a short circuit or electric leakage occurs due to the conductive portion 1. I am dealing with it so that it does not exist. The non-conductive portions 3 and 4 are all composed of knitted fabrics knitted only by non-conductive yarns such as synthetic fibers (for example, aramid fibers), natural fibers, and materials in which synthetic fibers and elastic yarns are mixed. Like the conductive portion 1, it is formed so as to be exposed on the front and back surfaces of the harness 2.

It should be noted that three or more conductive portions 1 may be provided in the band width direction of the harness 2 to separate them by the non-conductive portion 3, or only one may be provided in the band width direction of the harness 2. You may. Further, the non-conductive portion 4 may be provided on only one side of the conductive portion 1 or may not be provided.
Further, the conductive portion 1 can be formed in a linear shape instead of in a strip shape, or can be formed as a wide one forming the entire harness 2 in the band width direction and the band length direction (for these). Will be described later). In short, the arrangement and the number of conductive portions 1 are not limited at all. Further, the harness 2 itself is not limited to being formed in a band shape in the first place, and can be formed in a quadrangle such as a square or a rectangle.

In the harness 2 shown in FIG. 4A, it is naturally assumed that the two conductive portions 1 and 1 have conduction characteristics having low electrical resistance at both ends in the longitudinal direction of the band. Not only that, it is said that the band surface and / or the band back surface has a conduction characteristic with low electrical resistance even at an arbitrary position in the band longitudinal direction. Therefore, the magnitude of the electric resistance may be set according to the distance between the two points to be conducted in the band longitudinal direction of the conductive portion 1, or conversely, the length may be set according to the electric resistance. Alternatively, the magnitude of the electric resistance can be set by selecting whether the band width (number of courses) of the conductive portion 1 is widened or narrowed.

Further, in this harness 2, the two conductive portions 1 and 1 and the non-conductive portions 3 and 4 are integrally formed to have abundant elasticity along the longitudinal direction of the band, and the harness 2 is warped in the front and back directions. It has abundant flexibility to freely handle bending, bending to the left and right along the surface direction, and even twisting. Then, when the harness 2 is expanded and contracted in the longitudinal direction of the band, when it is warped or bent in the front-back direction, or when it is bent along the surface direction, and when these expansion and contraction, warping, and bending are repeated. Even so, the electrical resistance has the property of being held in an invariant state.

When knitting the conductive portion 1, the conductive yarn 10 and the elastic yarn 11 are mixed as shown in FIGS. 4 (B) and 4 (C). If the conductive thread 10 and the elastic thread 11 are included, it is optional to mix other kinds of threads.
The knitting structure that can be adopted for the conductive portion 1 is, for example, a smooth knitting (also referred to as double-sided knitting or interlock). The smooth knitting is a knitting structure in which two rubber knitting sheets are overlapped to fill the uneven grooves of each other. That is, when the upper surface side of FIG. 4B is set as the knitted fabric surface side and the lower surface side is set as the knitted fabric back surface side, the conductive yarn 10 is entwined with the conductive yarn old loop 10a on the knitted fabric surface side. One loop P1 is formed and shifts to the back side of the knitted fabric. Then, the second loop P2 is formed by being entwined with the conductive yarn old loop 10b on the back surface side of the knitted fabric, and thereafter, the third loop P3 is formed on the front surface side of the knitted fabric and the fourth loop P4 is formed on the back surface side of the knitted fabric. And so on. Therefore, the conductive threads 10 are provided in the knitted fabric of the conductive portion 1 in a zigzag shape in the front-back direction.

On the other hand, the elastic yarn 11 is entwined with the elastic yarn old loop 11a on the back surface side of the knitted fabric to form the first loop R1 and shifts to the front surface side of the knitted fabric. Then, the second loop R2 is formed by being entwined with the elastic yarn old loop 11b on the knitted fabric surface side, and thereafter, the third loop R3 is formed on the knitted fabric back surface side and the fourth loop R4 is formed on the knitted fabric surface side. Repeat such things as doing. Therefore, the elastic yarn 11 is also provided in the knitted fabric of the conductive portion 1 in a zigzag shape in the front-back direction. As a result, in the knitted fabric, the cross portions 13 of the conductive yarn 10 and the elastic yarn 11 are formed in an alternating arrangement for each loop.

However, while the elastic thread 11 has abundant elasticity, the conductive thread 10 hardly expands and contracts. Therefore, when the conductive portion 1 is extended along the surface direction of the front and back surfaces (the left-right direction in FIG. 4B, which is the same as the "course direction" described later), the elastic thread 11 is formed in the cross portion 13. By intersecting with the conductive yarn 10, the cross angle θ generated on the front and back sides of the knitted fabric is gradually expanded, and after a situation in which the angle becomes obtuse, only the elastic yarn 11 gradually stretches well.

Next, the conductive thread 10 is drawn from the loop to the cross portion 13 so as to be pulled by the elongation of the elastic thread 11.
Further, when the extension of the conductive portion 1 is released, only the elastic thread 11 in the cross portion 13 generates a tightening force due to contraction, and the conductive thread 10 receives the tightening force and pushes the conductive thread 10 from the cross portion 13 into the loops on both outer sides thereof. Occurs. The tightening force of the elastic thread 11 at this time has the effect of retaining the zigzag arrangement of the conductive thread 10 in the conductive portion 1 when not expanding and contracting, and giving a volume in the thickness direction.

In this way, the conductive thread 10 not only makes the loop smaller or larger by feeding or pushing it from the loop to the cross portion 13, but also expands and contracts together with the expansion and contraction of the elastic thread 11. As a result, the conductive portion 1 has elasticity as shown in FIG. 4 (C).
As is clear from this explanation, since the conductive thread 10 does not substantially expand and contract, the total length used in the course direction does not change, and the outer diameter thereof does not change. Not only that, the conductive threads 10 do not come into contact with each other in the loops arranged in the course direction, and do not get entangled or come into contact with each other between the plurality of courses. Therefore, the electrical resistance is also invariant.

Further, in the conductive portion 1, it can be said that the same course in the knitted fabric is separated into a constitutional path knitted by the conductive yarn 10 and a constitutional path knitted by the elastic yarn 11. Therefore, the influence (interference) of the expansion / contraction behaviors on each other's constituent paths is suppressed, and each of them becomes independent. Therefore, each of the constituent paths allows the expansion / contraction behavior with a high degree of freedom. As a result, abundant elasticity and flexibility are ensured as the conductive portion 1.

As is clear from the details described above, the conductive portion 1 provided in the harness 2 is a knitted fabric having abundant elasticity and flexibility and also having resilience when repeatedly stretched, but at the time of stretching. It has the property that there is no or no change in electrical resistance when it is not stretched. Therefore, in the case of wiring between a plurality of boards, the wiring path may have a complicated bend depending on the arrangement of each board, or the wiring length and the wiring path may not be determined until the wiring stage. As a suitable wiring member, when the boards move after wiring, or when a large expansion / contraction fluctuation occurs repeatedly in the wiring distance due to the operation of the moving body under the condition of wiring between the board and the moving body. It can be used.

Further, since the electric resistance does not change between the extended state and the non-extended state, it can be suitably used as a signal line that dislikes disturbance.
The conductive portion 1 causes the conductive yarn 10 to behave between the stretched state and the non-stretched state of the knitted fabric by being associated with the tightening force (contracting force) in the surface direction of the elastic yarn 11. Therefore, one of the features of the conductive portion 1 is that a metal wire can be used as the conductive thread 10 while exhibiting abundant elasticity (for example, 200% or more).

When a metal wire is used for the conductive yarn 10 in this way, the electric resistance can be suppressed to be much lower than that of the plated yarn or the like, and the voltage value and the current value that can be energized are increased without increasing the thickness of the knitted fabric. Also suitable for (can be made thin). Further, there is an advantage that the durability of the conductive portion and, by extension, the conductive portion 1 can be enhanced. Furthermore, the design can be enhanced and the development in terms of appearance can be widely expanded.
-Bioelectrode Next, the bioelectrode 20 that detects a bioelectric signal in close contact with the body surface of the detection site will be described. A schematic cross-sectional view of the bioelectrode 20 is shown in FIG. 4 (D). The bioelectrode 20 described in FIG. 4 and the bioelectrode 230 described in another figure are the same.

The bioelectrode 20 includes an electrode layer 21 composed of a fiber knitted fabric, and the surface roughness (Ra) of the fiber knitted fabric is 40 μm or less, preferably the fiber knitted fabric is made of conductive fibers. , The heat-bonded fibers or the heat-bonded fibers are included, and the conductive fibers and the heat-bonded fibers or the heat-bonded fibers are bonded to each other, and more preferably, the electrode layer 21 is the base material layer 22. It is provided above, and more preferably, the moisture permeation suppressing layer 23 is provided between the electrode layer 21 and the base material layer 22.

The bioelectrode 20 includes an electrode layer 21 as shown in FIG. 4D and as described above. The electrode layer 21 is made of a fiber knitted fabric.
The fiber knitted fabric constituting the electrode layer 21 has conductivity. From the viewpoint of imparting conductivity to the fiber knitted fabric, the fiber knitted fabric preferably contains conductive fibers. The conductive fiber is not particularly limited, and known fibers having conductivity can be used. Specific examples of conductive fibers include metal-plated fibers, conductive polymer fibers, metal fibers, carbon fibers, slit fibers, and conductive material-containing fibers. One type of conductive fibers may be used alone, or two or more types may be used in combination.

The metal-plated fiber is not particularly limited, and known ones can be used. For example, the surface of the synthetic fiber is coated with a metal such as silver, copper, gold, or stainless steel, or an alloy containing at least one of these. Examples include fibers that have been plated. Preferred examples of the synthetic fiber to be metal-plated include nylon fiber and polyester fiber.
The conductive polymer fiber is not particularly limited, and known ones can be used. For example, polystyrene sulfonic acid (poly4-styrene sulfonate; PSS) is added to poly 3,4-ethylenedioxythiophene (PEDOT). Examples thereof include PEDOT / PSS fibers using doped PEDOT / PSS, and fibers in which PEDOT / PSS and a matrix resin are composited. Examples of the matrix resin include polyvinyl alcohol (PVA) and the like. Further, the synthetic fiber may be impregnated with a conductive polymer. Examples of synthetic fibers include polyester fibers and nylon fibers.

The metal fiber is not particularly limited, and examples thereof include fibers composed of metals such as silver, nickel, copper, iron, and tin, or alloys containing at least one of these metals.
As the conductive material-containing fiber, a fiber composed of a fiber-forming polymer such as a polyester polymer or a polyamide polymer in which a conductive substance is uniformly dispersed (that is, a conductive polymer) is useful. Conductive substances include, for example, conductive carbon black such as furnace black, ketjen black, acetylene black, and channel black; simple substances such as silver, nickel, copper, iron, and tin; copper sulfide, zinc sulfide, and copper iodide. Metal compounds such as.

Among the conductive fibers, silver-plated nylon fibers, silver-plated polyester fibers, and fibers obtained by combining PEDOT / PSS with a matrix resin such as PVA are preferable.
The electric resistance value of the conductive fiber is not particularly limited, and examples thereof include about 0.1 to 100,000 Ω / 10 cm.
The fiber knitted fabric constituting the electrode layer 21 may be composed of only conductive fibers, or may further contain other fibers. As the other fiber, a heat-sealing fiber or a heat-bonding fiber (hereinafter, referred to as a heat-sealing fiber or the like) is preferably used. The difference between the heat-sealed fiber and the heat-bonded fiber may be distinguished by the strength of the bonding force generated by cooling from the semi-molten or softened state, and the one having the stronger bonding force is the heat-sealed fiber, and the fiber is bonded more than this. Those with weak force are heat-bonded fibers. This distinction is not clear and includes an ambiguous vague part, but the point is that any fiber can be used as long as it can bond the intersections of the fibers by heat treatment. For example, examples of polyurethane fibers as heat-sealed fibers include Mobilon R and Mobilon RL manufactured by Nisshinbo Textile Co., Ltd., and examples of polyurethane fibers that are also heat-sealed fibers and heat-bonded fibers are Asahi Kasei. An example is Loika SF manufactured by Co., Ltd. When the fiber knitted fabric further contains heat-sealed fibers and the like, the surface smoothness of the electrode layer 21 is improved (that is, by heat-pressing the electrode layer 21 containing the conductive fibers and the heat-sealed fibers and the like. , The surface roughness (Ra) can be reduced) to improve the adhesion to the skin (body surface). By enhancing the adhesion of the bioelectrode 20 to the skin, the bioelectric signal can be acquired with even higher accuracy.

The heat-sealed fibers are not particularly limited as long as they are bonded to each other by a hot press at, for example, about 80 ° C. or higher, but polyurethane fibers, nylon fibers, polyester fibers and the like are preferable. One type of heat-sealed fiber or the like may be used alone, or two or more types may be used in combination.
In this bioelectrode 20, the surface roughness (Ra) of the fiber knitted fabric is 40 μm or less. The surface roughness (Ra) of the fiber knitted fabric surface constituting the electrode layer 21 has such a small value, and the surface smoothness is very high. Therefore, the living body such as a situation where the body movement is large. Even in situations where artifacts are likely to be incorporated into electrical signals, it is possible to acquire bioelectric signals with high accuracy. More specifically, since the surface smoothness of the surface of the electrode layer 21 is very high, the bioelectrode 20 has high adhesion to the skin. As a result, the contact impedance between the skin and the electrode layer 21 is reduced, and as a result, artifacts are less likely to be incorporated into the bioelectric signal, and the bioelectric signal can be acquired with high accuracy. In addition, even if the body movement is not large, for example, even in a situation where it is difficult to sweat, artifacts are easily incorporated into the bioelectric signal. However, since the bioelectrode 20 has high adhesion to the skin, it is included in the bioelectric signal. It becomes difficult for artifacts to be taken in, and it becomes possible to acquire bioelectric signals with high accuracy.

Further, in the conventional bioelectrode, even when an electric stimulus is applied, the sensitivity of the bioelectrode 20 may be deteriorated and it may be difficult to apply the electric stimulus. Since the contact impedance between the two is reduced, the sensitivity is high, and it is possible to effectively apply electrical stimulation to the living body.
From the viewpoint of acquiring the bioelectric signal with higher accuracy, the surface roughness (Ra) on the surface of the fiber knitted fabric is preferably 35 μm or less, more preferably 30 μm or less, still more preferably 26 μm or less. From the same viewpoint, the surface roughness (Ra) is preferably 10 μm or more.

The surface roughness (Ra) on the surface of the fiber knitted fabric is a value measured by a method according to the provisions of JIS B0601-2001.
The thickness of the electrode layer 21 is not particularly limited, and examples thereof include about 10 to 1,000 μm, more preferably about 30 to 800 μm.
In the bioelectrode 20, for example, as shown in FIG. 4D, the electrode layer 21 is preferably provided on the base material layer 22. This makes it possible to improve the shape stability and mechanical strength of the bioelectrode 20.

The material constituting the base material layer 22 is not particularly limited, but a material having excellent flexibility is preferable from the viewpoint of improving the adhesion of the bioelectrode 20 to the skin. Examples of the material constituting the base material layer 22 include rubber such as chloroprene rubber and resins such as polyester, polyurethane and polyethylene. The material constituting the base material layer 22 may be one kind or two or more kinds. From the viewpoint of improving the adhesion of the bioelectrode 20 to the skin, when the base material layer 22 is made of a resin, the resin is preferably sponge-like.

The base material layer 22 may be a single layer or a plurality of layers. When the base material layer 22 is a plurality of layers, the materials constituting each layer may be the same or different.
The thickness of the base material layer 22 is not particularly limited, but is preferably 0.1 from the viewpoint of improving the shape stability and mechanical strength of the bioelectrode 20 and improving the adhesion of the bioelectrode 20 to the skin. About 10 mm, more preferably about 1 to 8 mm can be mentioned.

It is preferable that the bioelectrode 20 further has a water permeation suppressing layer 23 between the electrode layer 21 and the base material layer 22, as shown in FIG. 4D, for example. Since the water permeation suppressing layer 23 is provided in the bioelectrode 20, it is possible to more efficiently retain the water released from the skin between the skin and the surface of the electrode layer 21, and the living body. The electric signal can be acquired with even higher accuracy.

The water permeation suppressing layer 23 is not particularly limited as long as it can suppress the water permeation of the bioelectrode 20, and can be made of a resin film, a non-woven fabric, or the like. Examples of the material constituting the moisture permeation suppressing layer 23 include polyurethane, polyethylene terephthalate, acrylic resin, polyethylene, polypropylene, nylon and the like. Further, the moisture permeation suppressing layer 23 can be made of a non-woven fabric. The water permeation suppressing layer 23 may be a single layer or a plurality of layers. When the water permeation suppressing layer 23 is a plurality of layers, the materials constituting each layer may be the same or different.

The water permeability of the water permeation suppressing layer 23 is not particularly limited, but is preferably 200 g / m ² / h or less, and more preferably 150 g / m ² / h or less. The water permeability of the water permeation suppressing layer 23 is a value measured by the method of JIS L1099 (A-1 method).

The thickness of the water permeation suppressing layer 23 is not particularly limited, and examples thereof include about 1 to 500 μm, more preferably about 10 to 200 μm.
The method of laminating the electrode layer 21, the base material layer 22, and the water permeation suppressing layer 23 is not particularly limited, and examples thereof include a heat press and a method of providing the adhesive layer 24. For example, when the electrode layer 21 and the base material layer 22 are bonded by heat pressing, it is preferable to heat press them under the conditions of a temperature of about 80 to 200 ° C., a pressure of about 0.05 to 20 MPa, and about 1 to 60 seconds. When the electrode layer 21 and the moisture permeation suppressing layer 23 are bonded by heat pressing, it is preferable to heat press them under the conditions of a temperature of about 80 to 200 ° C., a pressure of about 0.01 to 10 MPa, and about 5 to 120 seconds. When the base material layer 22 and the moisture permeation suppressing layer 23 are bonded by heat pressing, they can be heat pressed under the conditions of a temperature of about 80 to 200 ° C., a pressure of about 0.01 to 10 MPa, and about 5 to 120 seconds. preferable.

Further, as a method of providing the adhesive layer 24, for example, a method of arranging a urethane non-woven fabric, a nylon non-woven fabric or the like between the layers and thermocompression bonding, or a method of using an adhesive such as a modified silicone polymer can be mentioned. When the adhesive layer 24 is provided, the thickness of the adhesive layer 24 is not particularly limited, and examples thereof include about 1 to 300 μm, more preferably about 10 to 200 μm.

The bioelectrode 20 may be further provided with layers other than these layers, if necessary. The total thickness of the bioelectrode 20 is not particularly limited, and examples thereof include about 0.1 to 12 mm, more preferably about 1 to 10 mm.
By connecting the bioelectrode 20 and a device for recording bioelectric signals with wiring or the like as described later, it is possible to acquire and record bioelectric signals such as electrocardiogram, electromyogram, electroencephalogram, and heart rate variability. It becomes.

Since the electrode layer 21 is made of a fiber knitted fabric, the bioelectrode 20 can be repeatedly washed and used, unlike a conventional bioelectrode having a conductive adhesive layer as an electrode, for example.
-Detailed structure of the headband (mounting structure of the conductive harness to the base material layer)
As described above, the conductive harness 200 is provided with two or more electrically independent constituent paths (4 here, but 1 may be 3 because it is a spare), and the detection means 220. Is selected so as to be different between the reference site S (A), the first site S (B), and the second site S (C) from these four constituent paths, and the bioelectrode 230 is electrically connected. including. More specifically, the detection means 220 is selected so as to be different between the reference portion S (A), the first portion S (B), and the second portion S (C) from these four constituent paths, and is electrically charged. It includes three terminal block boards 222 that are specifically connected and attached to the conductive harness 200, and a bioelectrode 230 that is electrically connected to the terminals of the terminal block board 222.

As shown in FIG. 3, in this headband 100, the terminal block substrate 222 is attached to the conductive harness 200, and the conductive harness 200 to which the terminal block substrate 222 is attached is joined to the annular base material layer 110. .. In the following, with reference to FIGS. 3 and 5, the terminal block substrate 222 is attached to the conductive harness 200, and the conductive harness 200 (to which the terminal block substrate 222 is attached) is attached to the annular substrate layer 110. After that, the attachment of the bioelectrode 230 to the terminal block substrate 222 will be described with reference to FIG.

As shown in FIG. 3, the annular base material layer 110 can be diverted from a known sports headband or the like, and a non-slip ring 112 made of a non-slip silicone gel or the like is formed inside. It is also preferable to provide. The annular base material layer 110 is not particularly limited as long as it has an annular shape having at least a part of elasticity, and the ratio of the annular base layer 110 having elasticity is 50% with respect to the total circumference. As mentioned above, it is preferably 80% or more. With this ratio, when the headband 100 is attached to the head H, the biological electrode 230 can be brought into close contact with the skin and the biological signal (electroencephalogram signal) can be detected with high accuracy.

Here, it is easily adjusted that the distance from the first part S (B) to the second part S (C) differs depending on the individual difference of the living body (even if the size of the head is substantially the same). Although a modification that can be performed will be described later, an annular base material layer 110 having a different peripheral length (diameter) is prepared so that the headband 100 can handle even a human body having a different head size in the first place ( For example, it is also preferable to manufacture three types of headbands for sports such as S, M, and L) and three types of headbands 100 having different sizes (diameters) in the unstretched state.

A 4-wire type is adopted for the conductive harness 200 (1 wire is a spare), and the detection circuits are made independent on the left and right sides of the head (electrically at the terminal board substrate 222A and the end 202 of the conductive harness 200). Since the brain wave signals (reference signals are common to the left and right) are detected at three locations on each side, as shown in FIGS. 3 and 5, the four conductive parts of the conductive harness 200 are detected. The predetermined terminals of the terminal board board 222 are electrically connected (soldered) to any one of 1, and the three terminals of the take-out board 240 are electrically connected to the three wires to which the terminal board board 222 is soldered. Is connected (soldered). Here, in order to electrically cut the conductive harness 200 at the back side portion of the terminal block substrate 222A substantially in the center and the end portion 202 near the center of the back of the head, the conductive harness 200 is left and right of the annular base material layer 110. It is structurally (physically) cut in half. Since the symmetrical conductive harness 200 is bonded to the annular base material layer 110 in this way, it is preferable in that the diameter of the headband 100 is uniformly expanded.

As shown in FIGS. 5 (A) to 5 (C) (and FIG. 6 described later), the terminal block board 222 has a male side (male snap 230A) of a metal snap button attached to an insulating board. .. It is sufficient that either one of the pair of metal snap buttons on the male side (male snap 230A) and the female side (female snap 230B) is attached to the insulating substrate (the headband 100 according to the present embodiment). The male side and female side of the snap button can be reversed).

Here, the snap button is a holder (so-called button) used for clothing or the like composed of a male side genko (convex) side and a female side spring (concave) side, and is an elastic member (here, here). The fitting member is not limited to the snap button as long as it has a concave portion including a spring) and a convex portion that is fitted into the concave portion and is held in a fitted state by an elastic member. Further, the biological signal detection device according to the present invention is not limited to such a snap button and the above-mentioned fitting member, and can be held in a detectable manner when the biological signal is detected and can be replaced when the biological signal is not detected. It may be a hook-and-loop fastener that can be easily removed.

In the terminal block board 222A (for the reference detection means 220A) shown in FIG. 5A of the terminal block board 222, the terminal 222T1 and the terminal 222T5 are electrically connected to the male snap 230A, and the terminal 222T1 and the terminal are connected. The 222T5 is electrically connected (soldered) to the conductive portion 1A of the conductive harness 200.
In the terminal block board 222B (for the first detection means 220B) shown in FIG. 5B of the terminal block board 222, the terminals 222T2 and 222T6 are electrically connected to the male snap 230A, and the terminals 222T2 The terminal 222T6 and the terminal 222T6 are electrically connected (soldered) to the conductive portion 1B of the conductive harness 200.

In the terminal block board 222C (for the second detection means 220C) shown in FIG. 5C of the terminal block board 222, the terminal 222T6 and the terminal 222T2 are electrically connected to the male snap 230A, and the terminal 222T6 And the terminal 222T2 are electrically connected (soldered) to the conductive portion 1C of the conductive harness 200.
As shown in the figure, the terminal block board 222C can be used upside down of the terminal block board 222B, and the spare terminal block board 222 can be used upside down of the terminal block board 222A.

Further, as shown in FIG. 5D, the take-out board 240 has terminals 240T1 and 240T5 provided on the insulating board, terminals 240T2 and 240T6, terminals 240T3 and terminals 240T7, and terminals 240T4. The terminals 240T8 are electrically connected (soldered) to each other, the terminal 240T1 is connected to the conductive portion 1A of the conductive harness 200, the terminal 240T2 is connected to the conductive portion 1B of the conductive harness 200, and the terminal 240T3 is connected to the conductive portion 1B of the conductive harness 200. Each is electrically connected (soldered) to the conductive portion 1C. Then, with respect to the take-out board 240, as shown in FIG. 2B, three lead wires 242 (six in total on the left and right) have terminals 240T1 (or terminals 240T5) and terminals 240T2 (or terminals 240T6). The lead wire 242 is electrically connected (soldered) to the terminal 240T3 (or the terminal 240T7), and the lead wire 242 is connected to the amplifier outside the headband 100, and the biological signal detected by the amplifier is amplified.

As shown in FIG. 3, the conductive harness 200 to which the terminal block substrate 222 and the take-out substrate 240 are electrically connected (soldered) in this way is joined to the annular base material layer 110. In this case, the detection circuits on the right side (R side) and the left side (L side) are made independent (electrically (structurally and physically) at the portion of the terminal block substrate 222A and the end portion 202 of the conductive harness 200. (Cut) The conductive harness 200 is bonded to the annular base material layer 110 with a heat-sealing tape (heat-welding tape, heat-bonding tape, etc.).

Here, in the headband 100 according to the present embodiment, the entire circumference of the annular base material layer 110 and the length of the conductive harness 200 in the unstretched state (from the right end 202 to the left side in FIG. 3). The conductive harness 200 is joined to the entire circumference of the annular base material layer 110 with substantially the same length up to the end portion 202), but the conductive harness 200 is joined to a part of the annular base material layer 110. (It is not limited to the headband to which the conductive harness 200 is bonded to the entire circumference of the annular base material layer 110). However, even in this case, it is preferable that the conductive harness 200 is bonded to the annular base material layer 110 at the positions of the terminal block board 222 and the take-out board 240.

Further, in this headband 100, the take-out substrate 240 is provided in the portion of the conductive harness 200 joined around the annular substrate layer 110, but the end portion 202 in FIG. 3 is further extended and extended. The take-out substrate 240 may be provided in the above. In this case, since the take-out substrate 240 can be provided far away from the human body (head H), for example, even if the human body turns over when detecting a biological signal (brain wave) at bedtime, a hard lead wire is formed. Since it is not on the subject's head, it does not feel strange even while sleeping, and biological signals (brain waves) can be acquired with high accuracy even overnight.
-Detailed structure of bioelectrode (mounting structure of bioelectrode to terminal block substrate)
As described above, the bioelectrode of the headband 100 in a state where the conductive harness 200 to which the terminal block substrate 222 and the take-out substrate 240 are electrically connected is bonded to the annular substrate layer 110 with reference to FIG. The attachment of 230 to the terminal block board 222 will be described. Note that FIG. 6A shows the bioelectrode 230 immediately before being attached to the terminal block substrate 222, FIG. 6B shows the bioelectrode 230 being attached to the terminal block substrate 222, and FIG. 6C shows the bioelectrode. 6 (D) is a perspective view of the plane P illustrated in FIG. 6 (C) as viewed from the direction X indicated by the arrow, after the 230 is attached to the terminal block board 222.

As shown in FIGS. 5 (A) to 5 (C) and FIG. 6, the fiber knitted fabric 232 constituting the electrode layer 21 included in the bioelectrode 230 has one side (here, here) provided on the terminal block substrate 222. A metal snap button (female snap 230B) on the other side (female side in this case) paired with the male side) is provided, and a hole 236 corresponding to the size of the male part 230A1 is provided, and the hole 236 is provided. The snap button on the male side (male snap 230A) and the snap button on the female side (female snap 230B) are fitted through the snap button, and the bioelectrode 230 is attached to the terminal block substrate 222. Here, at least the side (front side) of the bioelectrode 230 in contact with the skin must be composed of the fiber knitted fabric 232 constituting the electrode layer 21. Further, since the pair of snap buttons of the male snap 230A and the female snap 230B are made of metal and the female snap 230B is provided on the fiber knitted fabric 232 constituting the electrode layer 21, the male snap 230A and the female snap 230A and the female snap 230B are provided. After the 230B is fitted, the electrode layer 21, the female snap 230B, the male snap 230A, the predetermined terminal 222T of the terminal block substrate 222, and the predetermined conductive portion 1 of the conductive harness 200 are electrically conductive.

On the back side of the bioelectrode 230, a shock absorber 234 having elasticity such as a sponge is provided. As shown in FIG. 6D, the buffer 234 allows the fiber knitted fabric 232 constituting the electrode layer 21 to be brought into close contact with the skin, and a biological signal (brain wave) can be acquired with high accuracy. The vertical length of the bioelectrode 230 is about 3 to 4 times the vertical length of the annular base material layer 110, and as shown in FIG. 6D, the bioelectrode 230 is attached to the terminal block substrate 222. A shock absorber 234 is provided on the back side of the bioelectrode 230 by sticking or the like so as to come to a portion inside the annular base material layer 110 including the center in the vertical direction when attached to.

Hereinafter, the procedure for attaching the bioelectrode 230 to the terminal block substrate 222 will be described with reference to FIGS. 6 (A) to 6 (C).
As shown in FIG. 6A, the back side (buffer 234 mounting surface) of the bioelectrode 230 faces the terminal block substrate 222 (here, the terminal block substrate 222A), and the male portion of the male snap 230A 230A1 faces the hole 236.

Next, as shown in FIG. 6B, after the male portion 230A1 of the male snap 230A is passed through the hole portion 236, the female snap 230B moves from the front surface (outside) to the back surface (inside) of the annular base material layer 110. The bioelectrode 230 is wrapped around to the position of the male snap 230A. In FIG. 6B, the bioelectrode 230 wraps around the annular base material layer 110 from the upper side to the lower side, but conversely, the bioelectrode 230 may wrap around from the lower side to the upper side. ..

Next, as shown in FIG. 6C, the bioelectrode 230 is attached to the terminal block substrate 222 by fitting and fixing the female snap 230B to the male snap 230A via the hole 236. At this time, the size of the bioelectrode 230 (particularly the vertical length), the size and position of the shock absorber 234, the positions of the male snap 230A and the female snap 230B, and the positions of the female snap 230B so as to have the structure shown in FIG. 6 (D). , The size and position of the hole 236 are set.

<Biomedical signal detection method using headband>
In this way, the terminal block substrate 222 and the take-out substrate 240 are electrically connected to the conductive harness 200, the conductive harness 200 is bonded to the annular substrate layer 110, and the bioelectrode 230 is electrically connected to the terminal block substrate 222. The headband 100 shown in FIGS. 1 and 2 is completed. Hereinafter, a method for detecting a biological signal using the headband 100 will be described with reference to FIG.

First, the annular diameter of the conductive harness 200 joined to the annular base layer 110 and the annular base layer 110 of the headband 100 is artificially expanded (expansion step).
Next, after fitting the headband 100 with the annular diameter expanded to the head H of the human body, the artificial expansion is stopped and the headband 100 is attached to the head H of the human body (mounting step). At this time, the headband 100 is securely attached to the head H of the human body due to the elasticity of the annular base material layer 110 (and the conductive harness 200) (the detection portion due to the elasticity of the annular base material layer 110). It is preferable that the type (size) of the headband 100 is appropriately selected (so that the headband does not shift).

Next, as shown in FIG. 1C, the position of the first detection means 220B is aligned with the position of the forehead of the head H of the human body (first part S (B)) (first part determination step). , The position of the second detection means 220C is aligned with the position of the base of the auricle of the human body (second site S (C)), which is a predetermined position in the region S (second site determination step). At this time, since the annular base material layer 110 of the headband 100 and the conductive harness 200 have elasticity, the position can be changed even if the distance from the first part to the second part differs due to individual differences in the living body. Easy to adjust. Further, when the site adjustment step is completed in this way, the position of the reference detecting means 220A for detecting the reference biological signal is positioned at the reference portion S (A) in the substantially central portion of the forehead.

When the detection preparation is completed in this way, the potential difference between the left and right first parts S (B), which is the first biological signal in the forehead, which is the first part (S (B)), and the second part. The potential difference between the left and right second parts S (C), which is the second biological signal in the outer ear, which is (S (C)), is detected via an amplifier (detection step).
In this way, the biological signal of the first part and the biological signal of the second part whose position is different from that of the first part can be detected by one brace, so that it can be easily adjusted and can be adjusted. Biological signals can be detected with high accuracy.

When such a biological signal detection method is repeated, if the fiber knitted fabric 232 constituting the electrode layer 21 included in the biological electrode 230 is contaminated by sebum or the like on the human skin, it is difficult to detect the biological signal with high accuracy. become. In such a case, since the bioelectrode 230 and the terminal block substrate 222 are attached by snap buttons, they can be easily replaced.
<Action and effect of the headband according to the present embodiment>
As described above, according to the headband 100 according to the present embodiment, when the biological signal is detected from the biological electrode attached to the head of the human body and attached to the surface of the human body, the first portion ( The biological signal (brain wave) of the forehead) and the biological signal (brain wave) of the second part (ear) whose position is different from that of the first part, the distance from the first part to the second part due to individual differences in the living body. Even if they are different, the biological signal can be easily adjusted and the biological signal can be detected with high accuracy.

<Modification example>
In the following, the headband 101, which is a modification of the biological signal detection orthosis according to the present invention, will be described with reference to FIG. 7 corresponding to FIG. 3 described above and FIG. 8 corresponding to FIG. 1 described above. The headband 101 is different in that it includes two terminal block substrates 222C in addition to the configuration of the headband 100 according to the above-described embodiment. Other structures that are the same as those in the above-described embodiment are designated by the same reference numerals. The explanations thereof will not be repeated here because they overlap with the above explanations.

The headband 101 has a different distance L from the first site (S (B)) to the second site (S (C)) due to individual differences in the living body (L (1) ≠ L (in FIG. 8). In order to adjust 2)), at least one of the first detection means 220B and the second detection means 220C (second detection means 220C in this headband 101) was attached to the conductive harness 200. A plurality of (here, 3) terminal block boards 222C are provided, and the bioelectrode 230 is electrically connected to any one of the plurality of terminal block boards 222C.

More preferably, the headband 101 is worn on the head of a human body to detect a biological signal at the forehead (first site (S (B))) as a first biological signal and as a second biological signal. The terminal block substrate 222C constituting the second detection means 220C that detects the biological signal at the base of the auricle (the second part (S (C))) and detects the biological signal at the base of the auricle is a conductive harness. The 200 is provided with a plurality (3 in this case), and in the second detecting means 220C, the biological electrode 230 conforms to the position of the base of the auricle in the plurality of terminal block substrates 222C constituting the second detecting means 220C. It is electrically connected to any one terminal block substrate 222C.

More specifically, as shown in FIG. 7, the headband 101 has one terminal block substrate before and after the terminal block substrate 222C of the headband 100 shown in FIG. 3 (front and rear in the peripheral direction of the annular base material layer 110). 222C is further provided. The headband 101 is not limited to adding one terminal block board 222C before and after the terminal block board 222C of the headband 100, and is not limited to three terminal block boards 222C. .. That is, the headband 101 may be provided with two or more terminal block boards 222C with respect to the headband 100, and the position and number of the terminal block boards 222C to be added may be arbitrary (the number of the headbands 101 to be added may be arbitrary). 1 or more), they may be provided continuously, may be provided with intervals, and their intervals may be inconsistent. However, when the number of the terminal block boards 222C to be added increases, the elasticity of the annular base material layer 110 is lowered (since the terminal block board basically does not expand and contract even if the conductive harness 200 expands and contracts), it is preferable. Absent.

A biological signal detection method using the headband 101 having the above structure will be described with reference to FIG.
First, the annular diameter of the conductive harness 200 joined to the annular base layer 110 and the annular base layer 110 of the headband 100 is artificially expanded (expansion step).
Next, after fitting the headband 100 with the annular diameter expanded to the head H of the human body, the artificial expansion is stopped and the headband 100 is attached to the head H of the human body (mounting step). At this time, the headband 100 is securely attached to the head H of the human body due to the elasticity of the annular base material layer 110 (and the conductive harness 200) (the detection portion due to the elasticity of the annular base material layer 110). It is preferable that the type (size) of the headband 100 is appropriately selected (so that the headband does not shift).

Next, as shown in FIG. 8C or FIG. 8D, the position of the first detecting means 220B is aligned with the position of the forehead of the head H of the human body (first portion S (B)) ( First site determination step). At this time, the position of the reference detecting means 220A for detecting the reference biological signal is positioned at the reference portion S (A) in the substantially central portion of the forehead.
Next, among the plurality of terminal block boards 222C constituting the second detection means 220C, any one terminal block board 222C that best matches the position of the base of the auricle (second portion S (C)) is used. Select (selection step).

Next, the bioelectrode 230 is electrically connected to the selected terminal block substrate 222C by the procedure described with reference to FIG. 6 (connection step).
When the detection preparation is completed in this way, the potential difference between the left and right first parts S (B), which is the first biological signal in the forehead, which is the first part (S (B)), and the second part. The potential difference between the left and right second parts S (C), which is the second biological signal in the outer ear, which is (S (C)), is detected via an amplifier (detection step).

In this way, the headband 101, like the headband 100, can detect the biological signal of the first part and the biological signal of the second part whose position is different from that of the first part with one brace. Therefore, in addition to being easily adjustable and being able to detect biological signals with high accuracy, it has the following effects.
FIG. 8 (C) is the same figure (same subject) as in FIG. 1 (C), and has a length H (1) and a length L (1) as symbols. FIG. 8 (D) is a subject different from FIG. 1 (C), and has a length L (2) in addition to the reference numeral of FIG. 8 (C). Even if the subject shown in FIG. 8C and the subject shown in FIG. 8D have the same length H (1) indicating the size of the head (when the length H (1) is different). Since the relative positions of the outer ear with respect to the skull are different (the headbands of different sizes will be selected), the distance L between the first part S (B) and the second part S (C) is different. The subject shown in 8 (C) has a length L (1), and the subject shown in FIG. 8 (D) has a length L (2) (<L (1)).

When the headband 100 is attached to the subject shown in FIG. 8 (C), the second detection means 220C is positioned at an appropriate position of the second portion S (C), but FIG. 8 (D) shows. When the headband 100 is worn on the indicated subject, the second detection means 220C is not positioned at an appropriate position of the second portion S (C). In this case, the subject shown in FIG. 8D cannot detect the biological signal with high accuracy by the detection method using the headband 100.

On the other hand, in the headband 101 according to the present modification, for the subject shown in FIG. 8D, a plurality of terminal block substrates constituting the second detection means 220C in the selection step described above. In order to select one of the terminal block boards 222C that best matches the position of the base of the pinna (second part S (C)) among 222C (here, the frontmost terminal block board 222C is selected). It is possible to detect biological signals with high accuracy. Moreover, one of the terminal block boards 222C is selected from the plurality of terminal block boards 222C, and the bioelectrode 230 is electrically connected to the selected terminal block board 222C by simply connecting the bioelectrode 230 with a snap button. , The adjustment is extremely easy.

As described above, according to the headband 101 according to the present modification, when the biological signal is detected from the biological electrode attached to the head of the human body and attached to the surface of the human body, the first portion (forehead). ) Biological signal (brain wave) and the biological signal (brain wave) of the second part (ear) whose position is different from that of the first part, the distance L from the first part to the second part due to individual differences of the living body. Even if they are different, the biological signal can be easily adjusted and the biological signal can be detected with high accuracy.

It should be noted that the embodiments disclosed this time are examples in all respects and are not restrictive. The scope of the present invention is shown by the scope of claims rather than the above description, and is intended to include all modifications within the meaning and scope equivalent to the scope of claims.
For example, in both the headband 100 according to the above-described embodiment and the headband 101 according to the modified example, the fiber knitted fabric 232 constituting the electrode layer 21 was in contact with the skin via the buffer body 234, but (1). ) The male portion 230A1 of the male snap 230A may be brought into contact with the skin, or (2) the surface 230B1 of the female snap 230B may be brought into contact with the skin.

The present invention is preferably applied to a technique of detecting a biological signal from an electrode attached to a living body including a human body and attached to the surface of the living body, and the biological signal of the first part and a second part having a different position from the first part. It is particularly preferably applied to the technique of detecting the biological signal of the above-mentioned part with high accuracy even when the distance from the first part to the second part is different due to the individual difference of the living body.

1 Conductive stretchable knitted fabric 2 (for conductivity) Harness 3 Non-conductive part 4 Non-conductive part 20 Bioelectrode 21 Electrode layer 22 Base material layer 23 Moisture permeation suppression layer 24 Adhesive layer 100 Headband 101 Headband (modification example)
110 Cyclic substrate layer 220 Detection means 220A Reference detection means 220B First detection means 220C Second detection means 222 Terminal block substrate 222A (for reference detection means) Terminal block substrate 222B (for first detection means) Terminal Base board 222C (for the second detection means) Terminal block board 230 Bioelectrode 240 Extraction board

Claims (7)

A biological signal detection device that is attached to a living body and detects a biological signal of a first part in the living body and a biological signal of a second part whose position is different from that of the first part.
An annular substrate layer with at least a part of elasticity and
A first detection means provided at a position corresponding to the first portion in the ring and detecting a first biological signal for the first portion.
A second detection means provided at a position corresponding to the second portion in the ring and detecting a second biological signal for the second portion.
Elasticity that is electrically connected to the first detecting means and the second detecting means, and electrically flows a signal detected by the first detecting means and a signal detected by the second detecting means. Including with a conductive harness equipped with
The conductive harness is bonded to the base material layer ,
The conductive harness has a conductive portion knitted by mixing a conductive yarn and an elastic yarn and a non-conductive portion knitted only by a non-conductive yarn, and the conductive portion has a metal as the conductive yarn. Two or more electrically independent constituent paths using wires are provided.
Each of the detection means is a biological signal detection orthosis including a biological electrode selected so as to be different between a first portion and a second portion from the two or more constituent paths and electrically connected . The conductive harness has a conductive portion knitted by mixing a conductive yarn and an elastic yarn and a non-conductive portion knitted only by a non-conductive yarn, and the conductive portion has a metal as the conductive yarn. Two or more electrically independent constituent paths using wires are provided.
Each of the detection means
A terminal selected from the two or more constituent paths so as to be different between the first portion and the second portion, electrically connected, and attached to the conductive harness,
The biosignal detection orthosis according to claim 1, further comprising a bioelectrode electrically connected to the terminal. In order to adjust that the distance from the first part to the second part differs depending on the individual difference of the living body, at least one of the first detection means and the second detection means is attached to the conductive harness. Equipped with multiple attached terminals
The biological signal detection device according to claim 2 , wherein the bioelectrode is electrically connected to any of the plurality of terminals. The terminal comprises one side of a pair of metal snap buttons on the male and female sides.
The bioelectrode includes an electrode layer composed of a fiber knitted fabric, and the surface roughness (Ra) of the fiber knitted fabric is 40 μm or less.
The biological signal detection orthosis according to claim 3 , wherein the fiber knitted fabric is provided with a snap button on the other side paired with the one side. The fiber knitted fabric is provided with a snap button on the other side paired with the one side, and is provided with a hole corresponding to the size of the snap button on the male side .
The biological signal detection device according to claim 4 , wherein the male snap button and the female snap button are fitted through the hole, and the bioelectrode is attached to the terminal. The biological signal detection orthosis is attached to the head of a human body to detect a biological signal on the forehead as a first biological signal and a biological signal at the base of the auricle as the second biological signal.
A plurality of terminals constituting the second detecting means for detecting the biological signal at the base of the pinna are provided in the conductive harness.
In the second detection means, the bioelectrode is electrically connected to any one of the plurality of terminals constituting the second detection means that matches the position of the base of the pinna. The biological signal detection device according to any one of claims 2 to 5 . It is a biological signal detection method using a biological signal detection orthosis that is attached to the head of a human body and detects a biological signal on the forehead as a first part and a biological signal at the base of the auricle as a second part.
The biological signal detection device is
An annular substrate layer with at least a part of elasticity and
A first detection means provided at a position of a base material layer corresponding to the first site and detecting a first biological signal for the first site.
A second detection means provided at a position of the base material layer corresponding to the second portion and detecting a second biological signal for the second portion,
A stretchable harness through which a signal detected by the first detecting means and a signal detected by the second detecting means electrically flow, and a conductive harness bonded to the base material layer. Including
The conductive harness has a conductive portion knitted by mixing a conductive yarn and an elastic yarn and a non-conductive portion knitted only by a non-conductive yarn, and the conductive portion has a metal as the conductive yarn. Two or more electrically independent constituent paths using wires are provided.
Each of the detection means
A terminal selected from the two or more constituent paths so as to be different between the first portion and the second portion, electrically connected, and attached to the conductive harness,
Including a bioelectrode electrically connected to the terminal
The second detecting means includes a plurality of terminals attached to the conductive harness, and the bioelectrode is electrically connected to any of the plurality of terminals.
An expansion step for artificially expanding the annular diameter of the base material layer and the conductive harness bonded to the base material layer, and
After fitting the biological signal detection orthosis with the expanded ring diameter on the human head, the artificial expansion is stopped and the biological signal detection orthosis is attached to the human head.
The first part determination step of adjusting the position of the first detection means to the position of the forehead of the human body, and
A selection step of selecting one of the terminals constituting the second detection means that matches the position of the base of the auricle, and
A connection step of electrically connecting the bioelectrode to the selected terminal,
A method for detecting a biological signal, comprising a detection step of detecting a biological signal in the forehead, which is the first site, and a biological signal in the outer ear, which is the second site.