JP2022150935A - Garment for biological signal acquisition - Google Patents

Abstract

To provide a garment for biological signal acquisition that has achieved reduction of an uncomfortable feeling and acquiring of biological information accurately.SOLUTION: A garment for biological signal acquisition includes one or more electrodes 3 disposed on a reverse side of a garment body fabric 201 constituting a garment body 2, a connector 5 to which a receiver for receiving a biological signal acquired by the electrodes 3 can be connected, and a biological signal transmission part 4 for conducting the electrodes 3 and the connector 5. The garment body fabric is a mesh-like fabric having elastic property, and includes an elastic member 10 disposed on a front side at the electrode position of the garment body fabric, and a holding member 7 disposed on an opposite side of a garment body fabric side of the elastic member 10 for holding the elastic member 10 on the surface of the garment body fabric 201.SELECTED DRAWING: Figure 1

Description

The present invention relates to biosignal acquisition clothes for detecting biosignals from a living body.

In recent years, clothes equipped with a system capable of detecting biological signals (electrical signals from living bodies) from living bodies have been proposed. In order to acquire the wearer's biological information with high accuracy, it is necessary to bring the electrodes into close contact with the wearer's body. Therefore, in the case of a clothing-type biological information measuring device, a garment such as compression wear that strongly tightens the upper body is used as the clothing main body, and this tightening effect brings the electrodes into close contact with the body. This is because if the tightening is weak, the adhesion between the electrodes and the body is deteriorated, which causes a problem that the accuracy of biometric information is lowered (for example, heartbeat detection rate is lowered).

For example, Patent Literature 1 discloses a biosignal acquisition garment in which a cushion layer is arranged between the electrodes and the fabric of the body of the garment to enhance the adhesion between the living body and the electrodes. In the biological signal acquisition clothing, the clothing itself needs a certain amount of tightening force in order to secure the tightness.

JP 2019-58346 A

However, there is a problem that this tightening causes discomfort such as oppressive feeling to the wearer.

SUMMARY OF THE INVENTION The present invention provides a biosignal acquisition garment that achieves both reduction in discomfort and acquisition of biometric information with high accuracy.

The present invention provides one or more electrodes arranged on the back side of a garment main body fabric that constitutes the garment main body,
a connector connectable to a receiving device that receives the biosignal acquired by the electrode;
A biosignal acquisition garment including a biosignal transmission part that electrically connects the electrode and the connector,
The garment main body fabric is a stretchable mesh-like fabric,
an elastic member arranged on the front side of the electrode position of the garment main body fabric;
and a holding member arranged on the opposite side of the elastic member to the garment main body fabric side and holding the elastic member on the surface of the garment main body fabric.

In the present invention, the garment main body fabric is a stretchable mesh-like fabric, and includes an elastic member held on the surface side of the garment main body fabric by a holding member, thereby reducing discomfort caused by the tightening force of the garment main body fabric. It is possible to provide biosignal acquisition clothing that achieves both reduction and accurate acquisition of biometric information.

FIG. 1A is a schematic front view of a biological signal acquisition garment according to one embodiment of the present invention. 2A is a schematic front view showing the front side of the biosignal acquisition garment shown in FIG. 1, and FIG. 2B is a schematic front view showing the back side thereof. FIG. 3 is a cross-sectional view of the biological signal acquisition garment shown in FIG. 2A along line II. FIG. 4 is a schematic explanatory diagram of the biosignal receiver. 5A is a schematic cross-sectional view of the clothing body fabric, the elastic member, and the holding member when the biosignal acquiring garment shown in FIG. 1 is not worn, and FIG. 5B is the clothing body fabric, the elastic member, and the holding member when the garment is worn. is a schematic cross-sectional view of. FIG. 6 is a schematic diagram for explaining the dimensions of each component in the biosignal acquisition garment of the example. 7A and 7B are schematic front views of biosignal acquisition clothes of Comparative Examples 2 and 3, in which FIG. 7A shows the front side and FIG. 7B shows the back side. FIG. 8 is a cross-sectional view of the biological signal acquisition garment shown in FIG. 7A taken along line II-II. FIG. 9 is a schematic diagram for explaining the dimensions of each component in the biosignal acquisition garment of the comparative example. FIG. 10 is a graph comparing the heart rate detection rates obtained by having subjects wear the biological signal acquisition clothes of Examples 1 to 3 and Comparative Example 1. FIG. FIG. 11 is an explanatory diagram for explaining clothing pressure measurement points. FIG. 12 is a line graph showing the clothing pressure at measurement points when the biological signal acquisition clothing of Examples 1 to 3 and Comparative Examples 1 to 3 are worn. FIG. 13 is an explanatory diagram for explaining the measurement sites of the sensory test. FIG. 14 is a radar chart showing the results of the sensory test.

The inventors of the present invention have extensively studied how to achieve both reduction of discomfort caused by tightening force and acquisition of biometric information with high accuracy. As a result, a stretchable mesh-like fabric is used as the garment main body fabric to reduce the contact area between the garment main body fabric and the living body, and the elastic member locally increases the garment pressure when worn. The present inventors have found that by increasing the adhesion to the electrodes, the discomfort can be reduced and biometric information can be obtained with high accuracy. As used herein, the term "rear side or back side" refers to the side closer to the living body, and the term "front side or front side" refers to the side farther from the living body. "Upper" refers to the side closer to the neck, and "lower" refers to the side farther from the neck.

Hereinafter, embodiments of the present invention will be described in more detail based on the drawings. However, the invention is not limited to what is shown in the following drawings.

FIG. 1A is a schematic front view of a biosignal acquisition garment according to an embodiment of the present invention, FIG. 2A shows the front side of the biosignal acquisition garment shown in FIG. 1, and FIG. 2B shows the back side thereof. show. FIG. 3 is a cross-sectional view of the same biological signal acquisition garment taken along line II. FIG. 4 is a schematic explanatory diagram of the biosignal receiver. The biosignal acquisition garment 1 (innerwear) of this embodiment includes a garment body 2 , electrodes 3 , a biosignal transmission section 4 , and a connector 5 . An elastic member 10 is arranged on the front side of the electrode position of the garment body fabric 201, and the elastic member 10 is arranged between the garment body fabric 201 and the holding member 7 fixed to the garment body fabric 201, It is held on the surface of the garment body fabric 201 .

The electrodes 3 are arranged on the back side of the garment main body fabric 201 forming the garment main body 2, and are in contact with the living body (wearer's skin) to acquire biosignals from the living body. In this embodiment, there are two electrodes 3, which are arranged symmetrically in the regions covering both sides of the solar plexus, but the number of electrodes may be one or three or more. In addition, the location of the electrodes can be appropriately determined depending on the biological signal to be acquired, the biological tissue of interest, and the like. Examples of biological signals include signals due to pulse wave, pulse, respiration, body movement, and the like. Examples of measurement sites include the chest, back, and abdomen. When placed symmetrically in regions covering both sides of the solar plexus, heart rate and the like can be detected. Depending on the number of electrodes, the number of biosignal transmitters and connectors may be adjusted as appropriate.

The material of the electrode 3 is not particularly limited as long as it can acquire a biological signal. For example, it can be made of conductive fibers. As the conductive fiber, for example, a conductive metal-plated fiber obtained by plating a conductive metal on the fiber, a fiber impregnated with a conductive polymer, or the like can be used. Examples of conductive metals include silver, alumina, gold, and copper, and silver is preferable from the viewpoint of high conductivity. Although the fiber is not particularly limited, polyester fiber, nylon fiber, or the like can be used from the viewpoint of excellent durability. Conductive fibers can be used as an electrode by forming a fiber aggregate such as non-woven fabric, knitted fabric, and woven fabric. The fiber aggregate constituting the electrode 3 is not particularly limited, but may have a basis weight of 100 to 500 g/m ² , for example. The size and shape of the electrode 3 are not particularly limited as long as the biosignal can be acquired. For example, both the vertical and horizontal lengths of the electrodes 3 may be 1 to 10 cm. Also, the electrode 3 may have a thickness of, for example, 0.01 to 5 mm, although it is not particularly limited.

A part of the biosignal transmission part 4 is arranged on the surface side of the garment main body fabric 201 , and the electrode 3 side end part of the biosignal transmission part 4 penetrates the mesh hole of the garment main body fabric 201 and is connected to the electrode. 3, is electrically connected to the electrode 3, and transmits the biological signal acquired by the electrode 3. The biosignal transmission part 4 should just be able to transmit the biosignal which the electrode 3 acquired, and the material is not specifically limited. Like the electrodes 3, they can be made of conductive fibers. For example, the electrode 3 and the biosignal transmission unit 4 may be separate structures instead of being integrated. When the electrode 3 and the biosignal transmission part 4 are separate structures, the electrode 3 and the biosignal transmission part 4 may be joined by sewing with a conductive fiber thread, or the electrode 3 and the biosignal transmission part 4 may be joined with a conductive adhesive. The transmission section 4 may be adhered. The adhesive is not particularly limited, and for example, a hot melt adhesive or the like can be used. The electrode 3 and the biosignal transmission section 4 may be integrated (single structure), that is, the biosignal transmission section 4 may be configured by extending a part of the electrode 3 . Specifically, the biosignal transmission part 4 may be composed of the peripheral part and the projecting part extended from the electrode 3 . Also, the biosignal transmission unit 4 may be arranged on the back side of the garment main body fabric 201 .

The electrodes 3 and the garment main body fabric 201 may be fixed by sewing, or may be adhered with an adhesive such as a hot-melt adhesive. The biosignal transmission part 4 and the garment main body fabric 201 may be fixed by sewing, or may be adhered with an adhesive such as a hot-melt adhesive. When using a non-stretchable material for the electrodes, it is preferable to fix the electrodes in a state in which a margin for elongation is secured in advance in consideration of the elongation of the body fabric of the garment when worn. In other words, it is preferable that the electrodes 3 are fixed to the cloth of the body of the garment in a slightly loose state when the garment is not worn.

The connector 5 is a biosignal output unit for the biosignal receiver. The connector 5 has a connecting portion 51 arranged on the surface side of the biosignal transmitting portion 4 and a fixing portion 52 for fixing the connecting portion 51 to the biosignal transmitting portion 4. The connecting portion 51 and the fixing portion 52 are They may be arranged so as to sandwich the biosignal transmission section 4 . If the connector 5 is fixed to a portion of the biosignal transmission unit 4 that is arranged on the surface side of the clothing main body fabric 201 and is arranged on the surface side of the clothing main body fabric 201, the feeling of a foreign object caused by the connector 5 will be felt by the clothing body. It is preferable because it can be relieved by the fabric 201 . When sandwiching the biosignal transmission part 4 between the connection part 51 and the fixation part 52 , a conductive tape may be arranged between the fixation part and the biosignal transmission part 4 . As the connector 5, for example, a conductive metal snap button, magnet hook, or the like can be used.

When the biosignal transmission section 4 is arranged on the back side of the garment body fabric 201 , the connection section 51 and the fixing section 52 may be arranged so as to sandwich the garment body fabric 201 and the biosignal transmission section 4 . Further, in this case, in order to reduce noise other than the biosignal to be detected, on the back side of the biosignal acquisition garment 1, the biosignal transmission part 4 and the fixing part 52 of the connector 5 are made of an insulating sheet (not shown). It is preferably covered with From the viewpoint of reducing the feeling of a foreign object caused by the connector 5 , it is preferable that a cushion material (not shown) is arranged between the fixing portion 52 of the connector 5 and the insulating sheet 20 . The insulating sheet is not particularly limited as long as it has electrical insulation. Examples thereof include polyethylene terephthalate sheet, polyethylene naphthalate sheet, polyurethane sheet and the like. Examples of cushion materials include resin foams, and fiber aggregates such as knitted fabrics, woven fabrics, and non-woven fabrics.

As shown in FIG. 1, the garment main body fabric 201 is a stretchable mesh-like fabric, and is made up of a mesh hole portion 201a and a fiber portion 201b made of knitted fabric. Therefore, since the contact area between the body fabric 201 of the garment and the living body is small, the tightening feeling is alleviated as compared with the conventional compression wear, and in addition, the breathability is good, so that sweat is easily removed and the wearer is comfortable to wear. The planar shape of the mesh hole portion may be any shape such as a circle, an ellipse, a square, a rhombus, a polygon, and an irregular shape. The average area per mesh hole portion 201a is preferably 4 mm ² or more and 12 mm ² or less, and preferably 5 mm ² or more and 10 mm ² or less. The average area per mesh hole portion 201a can be calculated, for example, by spreading the fabric under no tension, taking a photograph, measuring the dimensions and shape, and calculating. Also, the area of the mesh hole portions 201a, the number in the field of view, and the area of the field of view are calculated, and using these values, the area ratio of the mesh hole portions 201a to the entire fabric can be calculated. Although the garment main body fabric 201 constituting the garment main body 2 is mainly the above-mentioned mesh-like fabric, part of the garment main body 2, for example, parts (shoulders, hem, etc.) that require higher strength than others, , It may be reinforced with a knitted or woven fabric other than the above-mentioned mesh-like fabric, or may be composed of the knitted or woven fabric.

The garment body fabric 201 is preferably a knitted fabric with high elasticity from the viewpoint of both comfort and accurate acquisition of biometric information. ) is preferably 80% or more and 200% or less, more preferably 90% or more and 150% or less. The transverse elongation (EMT) is preferably between 50% and 150%, more preferably between 50% and 80%. The elongation rate can be measured by the method described in Examples. In addition, from the viewpoint of both comfort and accurate acquisition of biometric information, the longitudinal elongation rate with respect to the lateral elongation rate is preferably 1.2 times or more and 2.5 times or less, and more preferably. is 1.5 times or more and 2.0 times or less. The knitting structure is preferably single raschel knitting. Such elastic fabrics can be composed of elastic fibers (threads) and non-elastic fibers (threads). Examples of elastic fibers include, but are not limited to, polyurethane elastic fibers, polyether-ester elastic fibers, polyamide elastic fibers, and polyolefin elastic fibers. Polyurethane elastic fibers are preferred from the viewpoint of excellent extensibility. The inelastic fibers are not particularly limited, but polyester synthetic fibers such as polyethylene terephthalate, polytrimethylene terephthalate and polybutylene terephthalate, and polyamide synthetic fibers such as nylon can be used.

It is preferable that the holding member 7 is made of a stretchable fabric having a lower stretchability than the garment main body fabric 201, for example, an elastic yarn mixed knitted fabric such as a power net. In general, power net fabric is a fine net-like knitted fabric with stretchability. strong in nature. The holding member 7 may be formed by laminating a plurality of power nets. The holding member 7 may be made of a fabric that is stretchable in one direction (a fabric that is substantially stretchable only in one direction) or a fabric that is stretchable in two directions. The elongation rate (EMT) of the holding member 7 in one direction (the same direction as the lateral direction of the garment body 2) is preferably 3% or more and 30% or less, more preferably 3%, from the viewpoint of accurately acquiring biological information. 15% or less. The elongation rate (EMT) of the holding member 7 in the other direction (the longitudinal direction of the garment body 2 or the same direction as the length direction) is not particularly limited, but is preferably 3% or more and 30% or less, more preferably It is 3% or more and 15% or less.

It is preferable that the holding member 7 and the portion of the garment main body fabric 201 facing the holding member 7 form a bag-like accommodation portion 71 , and the elastic member 10 is accommodated in the accommodation portion 71 . As shown in FIG. 1 , the accommodating portion 71 has an opening 72 that opens upward, so that the elastic member 10 can be taken in and out of the accommodating portion 71 . Therefore, by replacing the elastic member 10 with one having a different thickness, the degree of adhesion between the electrode 3 and the living body can be adjusted. For example, if the elastic member 10 is replaced with a thicker elastic member 10, the adhesion between the electrode 3 and the living body can be enhanced. In addition, in the biological signal acquisition garment 1, it is sufficient that the elastic member 7 can be held between the holding member 7 and the garment body fabric 201, and only the upper and lower two sides of the four sides of the holding member 7 are fixed to the garment body fabric 201. Alternatively, all four sides may be fixed to the garment main body fabric 201 to close the accommodating portion and prevent the elastic member 10 from being taken in and out. The holding member 7 may be fixed to the garment main body fabric 201 by sewing, or may be adhered with an adhesive such as a hot-melt adhesive. The fixing of the holding member 7 to the garment body fabric 201 may be continuous or intermittent on each side as long as the elastic member 10 is held between the holding member 7 and the garment body fabric 201. good too.

The material of the elastic member 10 is particularly limited as long as it is flexible and has an elastic repulsive force capable of urging the electrode 3 toward the living body when pushed toward the clothing body fabric 201 by the holding member 7 . no. For example, a rubber-like elastic body (elastic non-foaming body) or an elastic foam may be used, but an elastic foam is preferable because it is lightweight, and a sponge such as a cosmetic puff is preferable. The resilient foam can be an open cell foam, a semi-open cell foam, or a closed cell foam. Materials for elastic foam include natural materials such as sponge, natural latex, urethane (special urethane or wet urethane, etc.), latex, SBR (styrene butadiene rubber), PVA (polyvinyl alcohol) or NBR (acrylonitrile butadiene rubber), Synthetic materials such as silicon and olefin resin are exemplified. The compression resilience of the elastic member 10 is preferably 80% or more from the viewpoint of improving the adhesion of the electrode to the living body. Compression resilience can be measured, for example, by the method described in the Examples.

The size of the elastic member 10 can be appropriately adjusted according to the size of the electrode 3 . The vertical length and horizontal length of the elastic member 10 are not particularly limited, but may be in the range of 0.5 to 1.5 times the vertical length and horizontal length of the electrode 3, respectively. In the biosignal acquisition clothes, from the viewpoint of both comfort and accurate acquisition of biometric information, it is preferable that the clothing pressure is high in the part where the electrode 3 is provided and the clothing pressure is low in the other parts. It is preferable that there is a distribution in which there are high-pressure portions (portions where the electrodes 3 are present) and low-pressure portions (other portions). From the viewpoint of creating such a clothing pressure distribution, the thickness of the elastic member 10 is preferably 7 mm or more.

The clothing pressure (A) immediately below the electrode 3 is preferably 1.0 kPa or more, more preferably 1.4 kPa or more, from the viewpoint of accurately acquiring biological information. From the viewpoint of comfort, the average value (b) of the clothing pressure (B) other than directly under the electrode 3 in the waist circumference at the same position in the vertical direction as the electrode 3 is preferably 0.4 kPa or less, and more preferably 0.3 kPa or less. preferable. Although there is no lower limit for the average value, it is usually 0.1 kPa or more. Moreover, the ratio of the clothing pressure (A) of the electrode 3 to the average value (b) of the clothing pressure (B) is preferably 5 or more, more preferably 8 or more, from the viewpoint of wearing comfort. Although there is no particular upper limit for the ratio, 22 or less is appropriate. The clothing pressure (A) and the clothing pressure (B) can be measured by the method described in Examples.

The garment main body fabric 201 and the elastic member 10 may be fixed by sewing or adhesive, or may not be fixed.

FIG. 5A is a schematic cross-sectional view of the garment main body fabric 201, the elastic member 10, and the holding member 7 when the biosignal acquiring garment is not worn, and FIG. 7 shows a schematic cross-sectional view of FIG. As shown in FIG. 5A, when the garment is not worn, the elastic member 10 is preferably arranged between the holding member 7 and the garment body fabric 201 in an uncompressed state. As shown in FIG. 5B, tension is applied mainly in the waist width direction to the garment body fabric 201 and the holding member 7 when worn. Since the holding member 7 and the garment body fabric 201 are fixed to each other, the same tensile load acts on them. Since the bending rigidity of the fabric in this state is smaller for the garment body fabric 201 than for the holding member 7, the elastic member 10 is pressed by the holding member 7 toward the garment body fabric 20, that is, toward the electrode 3, and as a result, Adhesion between the electrode 3 and the living body is improved. If the elastic member 10 is arranged in an uncompressed state in the storage portion formed by the holding member 7 and the garment main body fabric 201 when not worn, the elastic repulsive force of the elastic member 10 is applied to the garment main body fabric when worn. It is preferable because it acts effectively on the 20 side.

As shown in FIG. 1, the bio-signal acquisition garment 1 may have a receiver 6 for receiving bio-signals. The biosignal receiver 6 receives the biosignal acquired by the electrode 3 and transmitted by the biosignal transmission unit 4, converts the biosignal into a digital signal, and transmits the digital signal, for example, by radio. It is a mobile terminal device. In this embodiment, as shown in FIG. 4, the biosignal receiver 6 has a connecting portion 61, and the connecting portion 61 and the connecting portion 51 of the connector 5 are detachably engaged with each other. , the biological signal receiver 6 and the connector 5 can be detachably connected. The biological signal receiving device 6 can be removed when the clothes are not in use, especially when they are washed.

FIGS. 1 to 3 exemplify the case where the biomedical signal acquisition garment 1 is a sleeveless shirt, but the biomedical signal acquisition garment 1 may be worn as long as it comes into contact with the living body. , short-sleeved shirts, long-sleeved shirts, girdles, and the like. By wearing the biological signal acquisition clothes 1, an electrocardiogram or the like can be continuously measured for a long period of time while carrying out daily life.

In order to prevent the garment from slipping up, the biosignal acquisition garment may have a band-shaped fastener made of an elastic material such as rubber arranged along the circumferential direction at part or all of the hem. .

Methods for measuring various parameters are as follows.
[Compression work (WC)]
Using a compression tester (Autograph AG-X plus 500N, manufactured by Shimadzu Seiki Co., Ltd., compressor size: diameter 100 mm), a load of 6.24 N and a speed of 1 mm / sec are applied to a pressurized area of 78.5 cm ² . Compression work (WC) was measured when the elastic member was pressed in the thickness direction.

[Compression resilience (RC)]
Compression tester (Autograph AG-X plus 500N manufactured by Shimadzu Seiki Co., Compressor size: diameter 100mm), pressurized area 78.5cm ² , load 6.24N, speed 1mm / sec. Compressive resilience (RC) when pressurized in the thickness direction was measured.

[Elongation rate (EMT)]
Using a precision universal testing machine (SHIMADZU Autograph AG-X plus manufactured by Shimadzu Corporation), under an atmosphere of room temperature 23 ± 1 ° C and relative humidity 50 ± 5%, the tensile speed (strain rate) is set to 12 mm / min. Tensile tests were performed on the pieces. In the tensile test, the load was measured while elongating the test piece until the load reached 2.45 N (maximum load), immediately recovered after reaching the maximum load, and the load was measured at the same speed during the recovery process. . The initial distance between chucks is 100 mm, the size of the test piece is 50 × 200 mm, the test is performed five times each in the horizontal direction and the vertical direction, and the elongation rate is calculated by obtaining the arithmetic average value in each direction. did.

EXAMPLES The present invention will be specifically described below using examples. In addition, the present invention is not limited to the following examples.

(Example 1)
As a garment body, outdoor underwear (Rafuma Millet Co., Ltd., DRYNAMIC NS CREW MIVO1248 men's polypropylene 66% nylon 28% polyurethane 6%, single raschel knitting, chest circumference 72 cm, average mesh hole area 8 mm ² , lateral elongation rate 65.63%, 118.52% longitudinal elongation) were prepared.

A woven fabric was produced using a conductive fiber (manufactured by Mitsufuji Co., Ltd.: "AGposs") obtained by plating nylon fiber with silver. Next, the fabric was cut to a predetermined size to prepare the electrode 3 and the biosignal transmission section 4, respectively. The dimensions of the electrode 3 and the biosignal transmission part 4 are such that the length of each part shown in FIG.
L1: 3.8 cm, L2: 0.5 cm, L3: 1.0 cm, L4: 1.8 cm, W1: 5.5 cm, W2: 5.3 cm, W3: 1.3 cm

As the elastic member 10, a synthetic rubber sponge (trade name: Foundation Puff square type, manufactured by Seria, compression work (WC): 8.48 gf·cm/cm ² , compression resilience (RC): 81.45%, thickness: 7 mm) was used. , as shown in FIG. 6B, prepared by cutting so that L5 is 4.0 cm and W4 is 5.4 cm.

FIG. 6C shows the power net used as the holding member 7 in the power net (trade name: ARCARE, product number: SACRO LIGHT-FX back stay part, 1-way power net, elongation rate: 4.89%). , was prepared so that L6 was 5.5 cm and W5 was 7.0 cm.

A biological signal acquisition garment 1 shown in FIGS. 1 to 3 was produced as follows. 1 to 3 do not show an adhesive, which will be described later.
First, a housing portion 71 for housing the elastic member 10 was formed on the surface side (the side opposite to the living body side) of the garment main body fabric 201 . Specifically, the holding member 7 is attached to the garment body fabric 201 so that the elastic direction of the holding member 7 is the same as the waist direction of the garment body, and is shaped like a bag having an opening at the top. sewn on. Next, after fixing the electrode 3 to the back side (living body side) of the garment main body fabric 201, the electrode 3 and the biosignal transmission section 4 were fixed. Specifically, the electrode 3 and the garment main body fabric 201 were aligned and overlapped so that the accommodation portion 71 was arranged directly above the electrode 3 , and the electrode 3 was sewn to the garment main body fabric 201 . Next, the side on which the connector 5 is provided in the longitudinal direction of the biosignal transmission part 4 is placed on the surface of the garment body fabric 201, the opposite side is passed through the mesh hole of the garment body fabric 201, and the end ( electrode side end) was sewn to the electrode 3 . Next, the snap button is arranged and fixed so that the convex part is on the front side of the biosignal transmission part 4 and the stop part is on the back side of the biosignal transmission part 4, thereby connecting the connection part 51 ( A connector 5 having a convex portion) and a fixing portion 52 (stopping portion) was formed. After that, the part of the biosignal transmission part 4 that was placed on the surface of the garment body fabric 201 was sewn to the garment body fabric 201 . A distance Da between the connecting portions 51 (convex portions) was set to 20 mm. Next, the elastic member 10 was inserted into the housing portion 71 to obtain the biological signal acquisition garment of Example 1 (chest circumference 72 cm, waist width 69 cm passing through the center of the electrode).

(Example 2)
The same configuration as in Example 1 except that the elastic member 10 was replaced with a synthetic rubber sponge having a thickness of 11 mm, a compression work (WC) of 20.67 gf·cm/cm ² , and a compression resilience (RC) of 82.89%. biosignal acquisition clothes (chest circumference 72 cm, waist width 69 cm passing through the center of the electrode).

(Example 3)
In the same manner as in Example 1, except that the elastic member 10 was replaced with a synthetic rubber sponge having a thickness of 15 mm, a compression work (WC) of 20.67 gf·cm/cm ² , and a compression resilience (RC) of 83.04%. As a result, the biological signal acquisition clothes of Example 3 (chest circumference 72 cm, trunk width 69 cm passing through the center of the electrode) were obtained.

(Comparative example 1)
A biological signal acquisition garment having the same configuration as that of Example 1 was produced, except that the elastic member 10 and its accommodating portion 71 were not provided.

(Comparative example 2)
As the biosignal acquisition garment of Comparative Example 2, a commercially available biosignal acquisition garment (trade name Smart Fit (registered trademark), manufactured by Kurashiki Boseki Co., Ltd., short-sleeved shirt, S size, chest circumference 78 cm, waist width passing through the center of the electrode 69 cm) were provided.

(Comparative Example 3)
As the biosignal acquisition garment of Comparative Example 3, a commercially available biosignal acquisition garment (trade name Smart Fit (registered trademark), manufactured by Kurashiki Boseki Co., Ltd., short-sleeved shirt, M size, chest circumference 80 cm, waist width passing through the center of the electrode 72 cm) were provided.

The biosignal acquisition clothes of Comparative Example 2 and the biosignal acquisition clothes of Comparative Example 3 have the same configuration except for the size of the clothes body. The structure, dimensions, etc. of clothes for biosignal acquisition of 2 and 3 will be described. 7 to 9 do not show an adhesive, which will be described later.

As shown in FIGS. 7 and 8, one or more electrodes 300 arranged on the back side of the garment main body fabric 20100 constituting the biosignal acquiring garment 100 and the garment main body 200 of Comparative Examples 2 and 3, and It has a connector 500 to which a receiving device for receiving biosignals acquired by the contacting electrode 300 can be connected, and a biosignal transmission unit 400 that electrically connects the electrode 300 and the connector 500 . A cushion layer 1000 is arranged between the electrode 300 and the garment body fabric 20100 . The connector 500 has a connecting portion 5100 arranged on the surface side of the garment main body fabric 20100 and a fixing portion 5200 for fixing the connecting portion 5100 to the garment main body 200 . and the biosignal transmission unit 400 are sandwiched therebetween. On the back side of the garment main body fabric 20100 , the biological signal transmission section 400 and the fixing section 5200 of the connector 500 are covered with an insulating sheet 2000 . A cushion layer 3000 is arranged between the fixing portion 5200 and the insulating sheet 2000 .

As the garment body fabric 20100, a 2-way shrinkable fabric (polyester fiber 82% by weight, polyurethane elastic fiber 18% by weight, longitudinal elongation 47.15%, lateral elongation 62.48%, basis weight 155 g/m ² , gauge 32G, tricot knit) was used.

The dimensions shown in FIG. 9A of the integrated body 7000 of the electrode 300 and the biosignal transmission part 400 are as follows. The material of the integrated body 7000 is a fabric (the weight per unit area is the same as that of Example 1) using conductive fibers (manufactured by Mitsufuji Co., Ltd.: "AGposs") obtained by plating silver on nylon fibers.
L10: 50mm, L20: 15mm, L30: 25mm, W10: 70mm, W20: 40mm, W30: 110mm, Da: 20mm

The material of the cushion layer 1000 and the cushion layer 3000 shown in FIG. 9B is double raschel (basis weight: 200 g/m ² , thickness: 2 mm) made of 100% by mass of polyester fiber, and the dimensions shown in FIG. 9B are as follows. be.
L40: 30mm, W40: 50mm, L50: 20mm, W50: 40mm
rice field.

The dimensions shown in FIG. 9C of the insulating sheet 2000 (manufactured by Poly Tape Co., Ltd.: "Poly Flex") are as follows.
L60: 60mm, L70: 40mm, W60: 240mm, W70: 60mm, W80: 100mm

The cushion layer 1000 and the electrode 300 are adhered with a polyurethane-based hot-melt adhesive, and the cushion layer 1000 and the biosignal transmission section 400 are adhered with the garment body fabric 20100 with a polyurethane-based hot-melt adhesive. The fixing portion 5200 of the connector 500 and the cushion layer 3000 are adhered with a polyurethane-based hot-melt adhesive. The insulating sheet 2000 is fused to the biosignal transmission section 400, the cushion layer 3000, and the garment body fabric 20100 by heat pressing. Lc was 200 mm in FIG. 7B.

(heartbeat detection rate)
Subjects (six males in their 20s) were asked to wear the biological signal acquisition clothes of Examples 1 to 3 and Comparative Example 1, and the following trials 1 to 4 were performed under an environment of 23 ± 1 ° C. and 50 ± 5%. An electrocardiogram was taken to measure the heart rate during exercise. Specifically, after wearing the clothes for biosignal acquisition, the left and right electrodes were wetted with about 0.1 mL of water, and after resting sufficiently, an electrocardiogram was measured while performing the following trials 1 to 4. In addition, an electrocardiogram was measured in the second lead (potential difference between left leg and right hand) using medical electrodes while performing similar trials. A BIOPAC MP160 electrocardiogram amplifier ECG100C was used as a measuring instrument.

[Attempt 1: Shoulder abduction]
After 2 seconds of standing still (starting posture), raise both arms to abduction 180° (final posture), hold still for 2 seconds in that state, and then return to standing still for 8 seconds each time. Do it 5 times.
[Attempt 2: Side bending]
After standing still (starting posture) for 2 seconds, laterally bend while raising one arm to 180° abduction (final posture), hold still for 2 seconds in that state, and then return to standing still for 8 seconds each time. and do it 5 times.
[Attempt 3: Forward bending]
After standing still (starting posture) for 2 seconds, bend forward (final posture), hold still for 2 seconds, and then return to standing still for 8 seconds each time. Repeat 5 times. .
[Attempt 4: Rotation]
After 2 seconds of standing still (starting posture), rotate the trunk to the left (final posture), hold for 2 seconds in that state, and then return to standing still for 8 seconds each time. Do 5 times.

The heart rate was counted from the obtained electrocardiogram, and the heart rate detection rate was calculated from the following formula.
Heart rate detection rate (%) = Heart rate (beats) measured by the power of clothes for biosignal acquisition/Heart rate (beats) measured by medical electrodes x 100

As shown in FIG. 10, the heartbeat detection rate is higher in Examples 1 to 3 with elastic members than in Comparative Example 1 without elastic members. Also, for example, looking at the results of Trial 3, the heart rate detection rate was 1.4 times that of Comparative Example 1, which did not include an elastic member, in Example 1, in which the thickness of the elastic member was 7 mm. In Example 2 in which the thickness is 11 mm, it is 1.6 times, and in Example 3 in which the thickness of the elastic member is 15 mm, it is 1.8 times. From this, it is presumed that the thicker the elastic member, the better the adhesion between the electrode and the living body (skin), and the electrode follows the living body during exercise, thereby improving the heart rate detection rate.

(Clothing pressure)
The clothing pressure when the biological signal acquisition clothing of Examples 1 to 3 and Comparative Examples 1 to 3 was worn on the ideal body (made by Keya, size: 91, model number: BG-733-01) shown in FIG. It was measured. As shown in FIG. 11, clothing pressure is measured at eight points along the horizontal direction on the left half of the body. The details of the clothing pressure measurement conditions are as follows.
[Clothing pressure measurement conditions]
・Experimental environment: Room temperature 23±1°C Humidity 50±5%
・Equipment used: Airbag type contact pressure measuring instrument (manufactured by AMI Techno)
・Sampling frequency: 5Hz
・Number of measurements: 3 times each ・Specification of measurement points: measurement point 3 is directly under the electrode, measurement point 1-3 distance 83 mm, measurement point 3-5 distance 106 mm, measurement point 5-8 distance 212 mm, measurement point 2 is equidistant from measuring points 1 and 3, measuring point 4 is equidistant from measuring points 3 and 5, the distance between measuring points 8-7, the distance between measuring points 7-6, and the distance between measuring points 6-5 distance is equidistant

Table 1 below shows the average values of three measurements of the clothing pressure (kPa), which are graphed in FIG.

As shown in Table 1 and FIG. 12, the clothing pressure directly below the electrode (measurement point 3) is higher in Examples 1 to 3 with elastic members than in Comparative Example 1 without elastic members. ing. Further, in Examples 1 to 3, the thicker the elastic member, the higher the clothing pressure at the measurement point 3. In Examples 1 to 3, the clothing pressure directly below the electrode (measurement point 3) was the same as in Comparative Examples 2 and 3, but the clothing pressure at other measurement points was lower than that in Comparative Examples 2 and 3. The average value (b) of the clothing pressure (A) at the measurement point 3 directly below the electrode and the clothing pressure (B) at the other measurement points is higher in Examples 1 to 3 than in Comparative Examples 2 to 3. (= clothes pressure (A)/mean value (b) of clothes pressure (B)) is large. From this, it can be seen that the biosignal acquisition clothes of Examples 1-3 are more comfortable to wear than the biosignal acquisition clothes of Comparative Examples 2-3. Also, the clothing pressure at the measurement point 3 in Examples 1 to 3 is the same value as the clothing pressure at the measurement point 3 in Comparative Examples 2 and 3, so it can be seen that biometric information can be obtained with high accuracy.

The reason why the clothing pressure at the measurement point 3 is higher than that at the other measurement points in the biosignal acquisition clothes of Comparative Examples 2 and 3 is that the fabric of the conductive fiber, which is the material of the electrode 3, is the fabric of the main body of the clothes. It is speculated that this is due to the fact that it is harder and has no stretchability, and that the cushion layer is arranged between the tightening force of the entire garment and the fabric of the main body of the garment and the electrodes.

(sensory test)
A sensory test was performed on the biological signal acquisition clothes of Examples 1 to 3 and Comparative Example 2 under the following conditions.
・Sensory test method: Scheffe's paired comparison method (Nakaya's modified method)
・Evaluation method: Wearing a sample, evaluation for each part while stationary and overall evaluation during movement ・Evaluation scale: 7 levels ・Evaluation trials: static standing, shoulder abduction, lateral bending, forward bending, rotation ・Experiment Environment: Room temperature 23±0.5℃ Humidity 50±5%
・Subjects: 7 males in their twenties ・Evaluation adjectives: (1) by region: no feeling of oppression, (2) overall: easy to move, feels good on the skin. , a side portion 84 and a back portion 85 .

As shown in FIG. 14, it has been confirmed that there is a significant difference in the evaluation of the feeling of pressure in terms of human senses at any evaluation site including the electrode part 82 .

The biological signal acquisition clothing of the present invention can achieve both comfort and accurate acquisition of biological information. Therefore, it is suitable for the elderly, children, sick and injured, etc. who dislike compression-type wear.

REFERENCE SIGNS LIST 1 biosignal acquisition garment 2 garment main body 3 electrode 4 biosignal transmitter 5 connector 6 biosignal receiver 7 holding member 10 elastic member 51 connector connection portion 52 connector fixing portion 61 biosignal receiver connection portion 71 housing portion 201 Garment body fabric 201a Mesh hole portion 201b Fiber portion

Claims (7)

one or more electrodes arranged on the back side of the garment body fabric constituting the garment body;
a connector connectable to a receiving device that receives the biosignal acquired by the electrode;
A biosignal acquisition garment including a biosignal transmission part that electrically connects the electrode and the connector,
The garment main body fabric is a stretchable mesh-like fabric,
an elastic member arranged on the front side of the electrode position of the garment main body fabric;
a holding member disposed on the opposite side of the elastic member from the garment main body fabric side, the holding member holding the elastic member on the surface of the garment main body fabric. 2. The garment for biosignal acquisition according to claim 1, wherein the garment main body fabric located opposite to the holding member has a bending rigidity smaller than that of the holding member when the garment for biosignal acquisition is worn. A portion of the garment main body fabric facing the holding member and the holding member form a bag-like accommodation portion,
3. The biological signal acquisition garment according to claim 1, wherein said elastic member is accommodated in said accommodating portion. The biosignal acquisition garment according to any one of claims 1 to 3, wherein the elastic member has a thickness of 7 mm to 15 mm. The biosignal acquisition garment according to any one of claims 1 to 4, wherein the holding member is a power net. The biosignal transmission unit and the connector are arranged on the surface side of the clothing main body fabric,
The biosignal acquisition according to any one of claims 1 to 5, wherein an electrode-side end portion of the biosignal transmitting portion penetrates a mesh hole in the fabric of the main body of the garment and is joined to the electrode. clothing. The biosignal according to any one of claims 1 to 6, wherein an average value of clothing pressure (B) other than directly under the electrode is 0.4 kPa or less in the waist circumference at the same position in the vertical direction as the electrode. clothing for acquisition.

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