JP2017029692A - Sensing wear - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a sensing wear for biological information measurement capable of measuring biological information even in a motion operation such as a walking operation or running.SOLUTION: There is provided a sensing wear obtained by arranging electrodes serving as body contact detection terminals, on an inside of clothing at which clothing pressure becomes equal to or more than 0.5 kPa, based on results of (1) modeling of a clothing material, (2) modeling of stitching and clothing wearing, (3) analysis of human body data, (4) and clothing wearing simulation. The sensing wear of the invention can stably measure a body electric signal even in a motion operation such as a walking operation or running.SELECTED DRAWING: None

Description

The present invention relates to a biological information measuring method using a sensor and a biological information measuring garment.
Furthermore, the present invention relates to a method for designing a garment for measuring biometric information using a sensor, and further relates to a method for providing a garment for measuring biometric information adapted to a customer's body shape using the design method. The present invention relates to a custom-made garment for measuring biometric information.

Conventionally, a method for measuring biological information of a human body such as an electrocardiogram is generally a method of detecting an electrical signal generated by a human body by fixing electrodes at 10 positions on the surface of the human body in a resting state. In order to do this, it is essential to use a gel or paste between the electrode and the skin surface, or to use an adhesive tape. For this reason, in long-time continuous measurement, unpleasant feeling due to sweating, itching and discomfort are generated, and a sticky electrode such as an adhesive tape is more likely to cause dermatitis.
Further, in the conventional measuring method, it is difficult to measure biological information due to electrode detachment due to increased sweating or displacement of the electrode position during exercise during an exercise operation such as walking or running. Further, during exercise, the electrode and the skin are rubbed, and the problems of discomfort, itching and discomfort, and dermatitis become more prominent.
In recent years, in the medical field and the health monitoring field, a wearable biological information measuring device that can easily measure biological information such as an electrocardiogram by being worn as clothes, a belt, or a strap has been attracting attention. For example, in a wearable measuring device that measures an electrocardiogram, it is expected that living information such as heartbeat fluctuations in various daily situations can be easily grasped by spending daily life while wearing it as clothes.

Such a wearable biological information measuring device generally includes an electrode, a sensor corresponding to various measurements, and wiring for transmitting those electric signals to an arithmetic / processing device or the like inside a garment made of woven or knitted fabric. ing.
As a technique for providing wiring in the wearable biological information measuring apparatus, a method of applying a paint containing a conductive polymer after masking a cloth in an area other than an area where an electrode or wiring is to be provided (Patent Document 1), etc. There is.

  However, when measuring biological information using a wearable biological information measuring device in which electrodes and / or other sensors are actually attached at arbitrary positions, the measurement subject in particular performs exercise motion such as walking motion or running (jogging). In the current state, the electrodes and / or other sensors are not in close contact with the skin, making it impossible to measure biological information or increasing noise in the measured biological information. The inventors of the present application have newly found that a problem occurs in that information to be obtained cannot be obtained.

  In the measurement of an electrocardiogram, Patent Document 2 (FIG. 1) describes that electrodes are attached to three positions on the front of the human body and one near the base of the neck, and Patent Document 3 (FIG. 1) describes that the human body. It is described that electrodes are mounted at two locations near the left and right ends of the left and right collarbones on the front surface and at two locations near the height of the left and right lowest ribs on the left and right axillary lines. Even when applied to the above, the above-mentioned problems during walking and exercise have not been solved.

JP, 2014-151018, A Special table 2012-519561 gazette JP 2006-61446 A

  The present invention has been made paying attention to the problems as described above, and its purpose is not to use gel, paste, adhesive tape or the like between the electrode and the skin surface, An object of the present invention is to provide a biological information measuring method and biological information measuring clothing that can be measured even during exercise.

As a result of intensive research to achieve the above object, the present inventors have found a new method for measuring biological information comprising electrodes at specific positions on the human body and have completed the present invention.
That is, the present invention has the following configuration.

[1] Sensing wear having a detection end in contact with a body surface on the inside of a garment,
(1) Modeling clothing materials,
(2) Modeling sutures and clothes,
(3) Analysis of human body data,
(4) Sensing ware having a detection end where a pressure due to clothing pressure found by performing clothing simulation is stably generated.
[2] The sensing wear according to [1], wherein the detection end is arranged at a location where the clothing pressure is 0.5 kPa or more.
[3] The detection end according to [1] or [2], wherein the detection end is arranged at a location where the variation in clothing pressure from 10 seconds after the start of exercise to 200 seconds is within 60% by a clothing simulation. Sensing wear.
[4] The sensing wear according to any one of [1] to [3], wherein the detection end is a skin contact electrode, and the area of each is 1 cm 2 or more.
[5] The sensing wear according to any one of [1] to [4], wherein the biological information to be measured is an electrocardiogram including at least an R wave.
[6] The sensing wear according to any one of [1] to [5], wherein the skin contact electrode includes a wiring, and the electrode and the wiring are made of the same material.

According to the biological information measuring method and biological information measuring garment of the present invention, it is not necessary to use gel, paste, adhesive tape or the like between the electrode and the skin surface, and measurement is also performed during walking or exercise. A biological information measurement method and a biological information measurement garment that can be provided can be provided.
In addition, according to the present invention, it is possible to provide a custom-made garment for measuring biometric information that fits individual body shapes of individuals. Various applications in the fields of sports medicine and sports physiology are considered as applications using the biological information measurement clothing. In these applications, it is assumed that a muscular body shape is assumed since it is an athlete who wears the clothing for measuring biological information. On the other hand, when considering applications in the medical field, nursing field, rehabilitation field, etc., the wearer is a general person and needs to deal with a wide range of body types such as the elderly, thin body owners, or obese bodies . Since the system of the present invention can provide custom garment for measuring biometric information fitted to an individual body shape, it is possible to more efficiently combine biometric information measurement and exercises such as treatment.

It is a figure which shows the clothing pressure fluctuation | variation examination position examined by simulation. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of a walk. It is a figure which shows the electrocardiogram at the time of rest and walking acquired in the position of 5. It is a figure which shows an example of the clothing for a biometric information measurement of this application. On the back side of the human body, electrodes and wiring are provided on the inner surface side of the clothing. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (1) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (2) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (3) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (4) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (5) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (6) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (7) in FIG. It is a figure which shows the clothing pressure fluctuation | variation simulation result at the time of the walk of the location of the clothing pressure fluctuation | variation examination result position (8) in FIG.

The present invention relates to a biological information measuring method, and more particularly to a biological information measuring method using an electrode.
The biological information in the present invention refers to biological information such as an electrocardiogram, electromyogram, body temperature, respiratory rate, and sweating that can be detected by an electrode and / or other sensor. The electrodes and / or other sensors are determined by biological information to be measured. Among these, it is preferable to provide an electrode capable of measuring an electrocardiogram. An electrocardiogram is information that can be recorded as a waveform by detecting electrical changes due to the movement of the heart via electrodes on the surface of a living body. Generally, time is plotted on the horizontal axis and potential difference is plotted on the vertical axis. Recorded as a waveform. The waveform that appears in the electrocardiogram for each heartbeat is mainly composed of five typical waves of P wave, Q wave, R wave, S wave, and T wave, in addition to this, U wave exists, and Q wave From the beginning of the wave to the end of the S wave may be referred to as a QRS wave. Among these waves, it is preferable to include an electrode capable of detecting at least an R wave. The R wave shows the excitement of the left and right ventricles and is the wave with the largest potential difference. The time from the top of the R wave to the top of the next R wave is generally referred to as RR time, but for one minute using the equation (heart rate) = 60 / (RR time (seconds)). The heart rate per hit can be calculated. That is, it is possible to know the heart rate by providing an electrode capable of detecting an R wave and detecting the R wave. In the present invention, QRS waves are also included in R waves unless otherwise noted.

  The electrode in the present invention has a function of detecting electrical information of a living body such as an electrocardiogram. In the biological information measuring method of the present invention, at least two electrodes are necessary. For example, taking an electrocardiogram as an example, the electrocardiogram can be detected by using at least two electrodes across the heart. The inventors of the present application have found that the position of the electrode is extremely important in the measurement of the biological information when the measurement subject of the biological information is in motion such as walking or running. That is, an attempt is made to measure biological information such as an electrocardiogram during exercise motion using clothing provided with electrodes, and when clothing having electrodes at any two positions across the heart is used, The contact with the body surface could not be ensured, and the electrocardiogram could not be measured, and it was impossible to properly measure the electrocardiogram even after trial and error by changing the electrode position.

As a result of intensive studies, the inventors of the present application have newly found out that biological information can be measured even when the subject is exercising by providing an electrode at a specific position on the surface of the living body. That is, the following electrode 1 and electrode 2 are provided as electrodes, and the electrode 1 is placed on the back surface of the human body at a distance of 10 cm from the back axillary line on the left side surface of the human body and on the back side of the human body. At least part of the region of the human body surface (region A) that satisfies the left-right position between the rear axillary line and the line parallel to the line (line 1) and the vertical position between the upper end of the seventh rib and the lower end of the ninth rib The electrode 2 is in contact with the electrode (electrode 1), and the electrode 2 is parallel to the posterior axillary line on the right side surface of the human body and the posterior axillary line located at a distance of 10 cm from the posterior axillary line and away from the back side of the human body. Electrode (electrode 2) in contact with at least a part of the region (region B) on the surface of the human body that satisfies the left-right position between the first line (line 2) and the vertical position between the upper end of the seventh rib and the lower end of the ninth rib It is.
The preferred left and right positions of the region A are a rear axillary line on the left side surface of the human body and a line (line 1) parallel to the rear axillary line located at a position on the human body surface at a distance of 5 cm away from the back side of the human body. The upper and lower positions of the preferred region A are between the upper end of the eighth rib and the lower end of the ninth rib. Similarly, the preferred position of the region B is that the right and left positions are parallel to the rear axillary line on the right side surface of the human body and the rear axillary line at a distance of 5 cm away from the back side of the human body. Between the upper end of the eighth rib and the lower end of the ninth rib.

In finding the appropriate positions of the electrode 1 and the electrode 2, the present inventors have studied a new simulation technique for clothing pressure during the movement operation according to the following steps (1) to (4), and based on the result. The proper position was estimated and verified. (1) Clothing material modeling, (2) Suture and clothing modeling, (3) Human body data analysis, (4) Clothing simulation.
As a result of the above-described simulation technique, it was estimated that pressure was always generated on the back side of the armpit during exercise. Next, as a result of further examination by the simulation technique in order to examine the optimum position, it was estimated that the pressure due to the clothing pressure is stably generated particularly at the positions 4 to 6 among the positions 1 to 8 in FIG. (FIG. 2). When an electrocardiogram was actually acquired at two positions on the left and right of the human body, a good electrocardiogram was obtained at rest and during walking (FIG. 3).

In the present invention, at least (1) modeling of clothing material,
(2) Modeling sutures and clothes,
(3) Analysis of human body data,
(4) Clothing simulation,
By predicting the pressure applied to the human body by clothing when it is stationary and exercising, i.e., clothing pressure, the location where the clothing pressure of a certain value or more is always expected to be generated is determined as the detection end electrode placement region candidate of the sensor. can do.
In the present invention, it is preferable that a position where the clothing pressure predicted by the above procedure is 0.5 kPa or more is a candidate for the detection end electrode arrangement region, and a place where the clothing pressure is 0.6 kPa or more is a candidate for the detection end electrode arrangement region. Further, it is preferable that a portion of 0.7 kPa or more is a candidate for the detection end electrode arrangement region, and a portion of 0.8 kPa or more is preferably a candidate for the detection end electrode arrangement region. If the clothing pressure falls below this range, the contact between the detection end electrode and the human body may become unstable during intense exercise, and biological information may not be acquired.
On the other hand, if the clothes pressure is 3.0 kPa or more, preferably 2.5 kPa or more, and more preferably 2.0 kPa or more, the clothes will be felt tight, which is not preferable.
Furthermore, in the present invention, it is preferable that the pressure variation in the region where the detection end electrode is arranged is small. In the present invention, it is preferable that the temporal variation in pressure at the same position during exercise assuming an exercise operation is 60% or less, more preferably 50% or less, and still more preferably 40% or less. preferable. If the pressure variation exceeds this range, the contact between the detection end electrode and the human body may become unstable during intense exercise, and biological information may not be acquired.
Here, the pressure variation (%) is the pressure variation (%) of the change over time in clothing pressure obtained during exercise = 100 × (clothing pressure maximum value−clothing pressure minimum value) / clothing pressure arithmetic average value.
Also, immediately after the start of exercise, clothing may be greatly displaced as the body shape changes, so it is important to read clothing pressure and variation in a state that is stabilized to some extent. Specifically, the determination may be made based on the clothing pressure and variation between 10 seconds after the start of exercise and 200 seconds after simulation.

For modeling (1) clothing material in the present invention, the finite element method and the constitutive law of the fabric (superelastic anisotropy (superelasticity + river model) can be used.
In modeling clothing materials, it is necessary to consider the anisotropy and nonlinearity of the materials, and a superelastic base material (shell) + river model can be used as the clothing material. As a method for measuring and describing material anisotropy, a method known as the Kawabata method can be applied. The Kawabata method is a fiber material evaluation method published in “Standardization and analysis of texture evaluation (2nd edition)” issued by the Japan Textile Machinery Society, Texture Measurement and Standardization Research Committee.

For modeling (2) stitching and clothing in the present invention, first, a pattern model showing a two-dimensional shape of a pattern of clothes to be virtually worn on a human body model is created, and the pattern model is divided into a plurality of elements, Each element is given the mechanical characteristics indicated by the cloth model, and the pattern model is deformed by solving the equation of motion of each element using a finite element method, and the clothes are virtually attached to the human body model. Can be modeled.

(3) The analysis of human body data means a method for modeling human body shape and responding to deformation of the human body during exercise. As an example of human body data modeling, based on the data obtained as a result of measuring body dimensions of 178 items of 34,000 people nationwide conducted by the Human Life Engineering Research Center (HQL), Natural average that is not corrected by foundation based on "average human body size dummy", which is imaged by adding three elements of anatomical knowledge and aesthetics to the average value of each part of human body, and also based on "average human body size dummy" Three-dimensional measurement of “Natural nude body for cutting” considering the body shape and natural posture, and data modeled as a rigid body can be used. The data that can be used as the human body data is not limited to this, and a human body shape corresponding to the country, ethnic group, sex, and age may be prepared and used. In addition, when a customer's personalized clothing for measuring biometric information is required, data obtained by modeling a customer's body shape three-dimensionally can be used.
In the present invention, it is preferable to predict the clothing pressure by obtaining the clothing pressure during exercise as well as at rest. As a human body model at the time of exercise, target exercises such as jogging, short distance running, racewalking, long jump, running high jump, hammer throwing, shot throwing, throwing, etc., gymnastics competition such as iron bars, floor exercises, jumping horses, parallel bars, Sports such as baseball, soccer, basketball, volleyball, etc., sports using bicycles and other traveling equipment, mountain climbing such as rock climbing, bouldering, winter sports such as speed skating, figure skating, skiing, snowboarding, automobile competition, motorcycle The movement of the human body during motor sports such as competitions is measured using Autodesk Maya (R) MotionBuilder (R), etc., or the movement amount of each part of the human body is obtained using motion capture technology, etc. You can exemplify how to correct the shape and place it in time series The In this case, the human body is deformed along the time axis, but at each moment, the human body behaves as a rigid body. Exercise includes general movements in daily life and work movements during work.
(4) Clothing simulation.
The clothing simulation is performed using the human body shape modeled by the above method. Each element of the pattern divided into a plurality of elements in the modeling of stitching and clothing is transformed into the pattern model by solving the equation of motion of each element using a finite element method, and the clothes are converted into the human body model. Since it virtually collides with the human body on the assumption that it is virtually worn, it is possible to calculate the clothing pressure that the worn clothing virtually exerts on the human body model.
In addition, by wearing thin clothes on a complicated human body surface shape, the calculation result becomes unstable when “wrinkles” occur as a result of clothing simulation or when a loose gap occurs between the human body and the clothes. In this case, the calculation result can be stabilized by applying the artificial viscosity method on the premise that the dissipated energy is sufficiently small with respect to the total strain energy of the clothes.
In addition, in the case of calculation using a human body model in which the posture of the movement process changes, the artificial viscosity method may not function properly. In this case, on the assumption that the condition that the kinetic energy is sufficiently small with respect to the total strain energy of the clothes is satisfied, the clothing simulation can be performed by calculating as a quasi-static dynamic analysis.

For the garment material modeling, stitching and garment modeling, and static garment simulation in the present invention, more specifically, a method disclosed in Japanese Unexamined Patent Application Publication No. 2009-230563 can be used. For dynamic simulation, Journal of the Textile Machinery Society Vol.68, No.5 (2015) p.242-243. Journal of the Textile Machinery Society Vol.68, No.5 (2015) p.244-245. Can be used.

  In the present invention, in addition to the electrode 1 and the electrode 2, the electrode 3 is preferably used as a ground electrode. When the electrocardiogram is measured, since the electrocardiogram signal is a very weak signal, it is important that the ground electrode serving as a reference is stable. As a human body surface position where the electrode 3 is used, A position where the muscle mass is relatively small is preferable in order to prevent electric noise from being mixed. Specifically, the electrode 3 is located between the upper end and the lower end of the eleventh rib at least on either the left or right side of the front surface of the human body. It is preferable to contact at least a part of the region (region C). Moreover, in this invention, electrodes other than the said electrodes 1-3 can be further provided.

In the present invention, the electrode preferably includes a conductive layer capable of detecting electrical information of a living body, and further includes an insulating layer. The electrode has an area necessary for detecting electrical information of a living body such as an electrocardiogram, and the area of each electrode is preferably 1 cm ² or more. More preferably, it is 5 cm ² or more, more preferably 10 cm ² or more, and particularly preferably 20 cm ² or more. Although an upper limit is not specifically limited, 100 cm < ² > or less is preferable.
The shape of the electrode can be any shape such as a square, a triangle, a pentagon or more polygon, a circle, and an ellipse.

  The electrode in the present invention preferably has elasticity so that it can follow the movement of the person being measured. For example, a conductive composition containing a fibrous electrode including a conductive polymer obtained by coating a base fiber with a conductive polymer by impregnation or the like, a conductive filler such as metal powder, and a resin containing stretchability By using a sheet-like electrode formed from the above, an electrode having stretchability can be obtained. Among these, since the sheet-like electrode formed from the conductive composition can use a component having high conductivity such as metal powder, the electrical resistance value is lower than that in the case of using a conductive polymer. It is preferable because it can be obtained and a weak electric signal can be detected. The electrical resistance value on the electrode surface is preferably 1000 Ω / cm or less, more preferably 300 Ω / cm or less, further preferably 200 Ω / cm or less, and particularly preferably 100 Ω / cm or less. In the sheet-like electrode formed from the conductive composition, the electrical resistance value on the electrode surface can be suppressed to a range of 300 Ω / cm or less.

  In addition, since the electrode formed from the conductive composition has a low electric resistance value, the wiring and the electrode can be made of the same material, which is a preferable embodiment of the present invention. When the wiring and the electrode are made of the same material, the wiring width may be 1 mm or more, and more preferably 5 mm or more and 10 mm or less.

  In the present invention, it is preferable that biological information is measured by clothing including the electrode 1 in contact with at least a part of the region A and the electrode 2 in contact with at least a part of the region B. The form of the garment is not particularly limited, and garments in the form of sportswear, T-shirts, polo shirts, underwear, nightclothes, cutter shirts, lab coats, and the like can be used. The electrode 1 that contacts at least a part of the region A and the electrode 2 that contacts at least a part of the region B are provided inside the garment, and biological information is measured by wearing them.

The electrode used in the present invention preferably further has an insulating layer. For example, a sheet-like form including a first insulating layer and a conductive layer can be used. Moreover, the wiring used by this invention can use the sheet-like thing containing a 1st insulating layer, a conductive layer, and a 2nd insulating layer, for example.
Hereinafter, an example in which the electrode and the wiring are made from the same material and a sheet in which the electrode and the wiring are integrated, which is a preferred embodiment of the present invention, will be described.

(First insulation layer)
In this invention, a 1st insulating layer is an adhesive surface at the time of laminating | stacking an electrode and a wiring sheet on a base material, and the water | moisture content from the other side of the base material on which the 1st insulating layer was laminated | stacked on a conductive layer at the time of wear Prevent reaching. In addition, the conductive layer described later in the present invention has good extensibility, but when the substrate is a material rich in extensibility exceeding the extensibility of the conductive layer, the conductive layer follows the elongation of the substrate and becomes conductive. It is also conceivable that the layer is stretched and as a result cracks occur. In a state where the first insulating layer is laminated on the garment, the first insulating layer also serves to prevent the garment from stretching and to prevent the conductive layer from being excessively stretched.

  The resin forming the first insulating layer is not particularly limited as long as it is an insulating resin. For example, polyurethane resin, silicone resin, vinyl chloride resin, epoxy resin, polyester elastomer, etc. It can be preferably used. Among these, polyurethane resins are preferable from the viewpoint of adhesiveness with the conductive layer. In addition, 1 type of resin which forms a 1st insulating layer may be sufficient, and 2 or more types may be sufficient as it.

  In the first insulating layer of the present invention, the insulating resin is dissolved or dispersed in an appropriate solvent (preferably water), and applied or printed on a release paper or release film to form a coating film, It can be formed by evaporating and drying the solvent contained in the coating film. Moreover, the commercially available sheet | seat thru | or film which has the appropriate physical property mentioned later can also be used.

  The film thickness of the first insulating layer is preferably 200 to 20 μm, more preferably 150 to 50 μm. If the first insulating layer is too thin, the insulating effect and the anti-elongation effect will be insufficient. On the other hand, if the first insulating layer is too thick, the stretchability will be hindered and the overall thickness of the electrode and wiring will be increased in the manner of being laminated on clothing. There is a risk of impediment to comfort.

(Conductive layer)
In the present invention, a conductive layer is preferably formed on the first insulating layer. This conductive layer ensures conduction.
The conductive layer preferably contains a conductive filler and a resin.

  The conductive filler that forms the conductive layer is preferably a metal powder. Moreover, conductive materials other than metal powder and metal nanoparticles can be used as the conductive filler as necessary.

  Metal powders include precious metal powders such as silver powder, gold powder, platinum powder and palladium powder, base metal powders such as copper powder, nickel powder, aluminum powder and brass powder, as well as different types of particles made of inorganic materials such as base metal and silica. Examples thereof include a plating powder plated with a noble metal, a base metal powder alloyed with a noble metal such as silver. Among these, silver powder and copper powder are preferable from the viewpoint of easily exhibiting high conductivity and price, and it is desirable that silver powder and / or copper powder be the main component (50% by mass or more). In addition, only 1 type may be sufficient as an electroconductive filler, and 2 or more types may be sufficient as it.

  Preferred shapes of the metal powder include known flaky shapes (flaky shapes), spherical shapes, dendritic shapes (dendritic shapes), and agglomerated shapes (shapes in which spherical primary particles are aggregated three-dimensionally). . Among these, flaky, spherical, and aggregated metal powders are particularly preferable.

  The average particle size of the metal powder is preferably 0.5 to 10 μm. If the average particle diameter is too large, it may be difficult to form a desired pattern shape when attempting to form a wiring with a fine pattern. On the other hand, if the average particle size is too small, the metal powder tends to aggregate during formation of the conductive layer, and the raw material cost increases as the particle size decreases, which is not preferable.

The proportion of the metal powder in the conductive filler is preferably 80% by volume or more, more preferably 85% by volume or more, and still more preferably 90% by volume or more. If the content ratio of the metal powder is too small, it may be difficult to develop sufficiently high conductivity.
In the present invention, the volume% of each component is obtained by measuring the mass of each solid content of each component contained in the paste and calculating (the mass of each solid content / the specific gravity of each solid content) to calculate the solid content of each component. It is calculated | required by calculating the volume of.

  As other conductive materials, for example, carbon nanotubes are preferably mentioned, and in particular, the surface has a mercapto group, an amino group, a nitrile group, or a surface treatment with a rubber containing a sulfide bond and / or a nitrile group. Preferably it is. In general, a conductive material itself has a strong cohesive force, and a conductive material having a high aspect ratio has a low dispersibility in the resin, but has a mercapto group, an amino group or a nitrile group on the surface, a sulfide bond and / or a nitrile group. Due to the surface treatment with the rubber containing, the affinity for the metal powder is increased, an effective conductive network can be formed together with the metal powder, and high conductivity can be realized.

  The proportion of the conductive material in the conductive filler is preferably 20% by volume or less, more preferably 15% by volume or less, and still more preferably 10% by volume or less. If the content of the conductive material is too large, it may be difficult to uniformly disperse it in the resin, and the conductive material as described above is generally expensive.

  Examples of the metal nanoparticles include silver, bismuth, platinum, gold, nickel, tin, copper, and zinc, and the average particle diameter is preferably 2 to 100 nm. In particular, from the viewpoint of conductivity, copper, silver, platinum, and gold are preferable, and those containing silver and / or copper as a main component (50% by mass or more) are more preferable. Inclusion of metal nanoparticles can be expected to improve conductivity, contribute to rheology adjustment of the conductive paste used to form the conductive layer, and improve printability.

  The proportion of the metal nanoparticles in the conductive filler is preferably 20% by volume or less, more preferably 15% by volume or less, and still more preferably 10% by volume or less. If the content of the conductive material is too large, it may easily aggregate in the resin, and metal nanoparticles having a small particle diameter as described above are generally expensive. Is desirable.

  The amount of the conductive filler in the conductive layer (in other words, the amount of the conductive filler in the total solid content of the conductive paste for forming the conductive layer) is preferably 15 to 45% by volume, more preferably 20 ~ 40% by volume. If the amount of the conductive filler is too small, the conductivity may be insufficient. On the other hand, if the amount is too large, the stretchability of the conductive layer tends to decrease, and the resulting stretchable electrode and wiring sheet are stretched. As a result, cracks and the like may occur, and as a result, good conductivity may not be maintained.

  The resin forming the conductive layer preferably contains at least a rubber containing a sulfur atom and / or a rubber containing a nitrile group. Sulfur atoms and nitrile groups have a high affinity with metals, and rubber is highly stretchable and can prevent cracks and the like even when stretched. It can be maintained in a dispersed state to exhibit excellent conductivity. A rubber containing a nitrile group is more preferable from the viewpoint of a change in electric resistance during elongation. In addition, only 1 type may be sufficient as resin which forms a conductive layer, and 2 or more types may be sufficient as it.

  The rubber containing a sulfur atom is not particularly limited as long as it is a rubber or elastomer containing sulfur. The sulfur atom is contained in the form of a sulfide bond or disulfide bond of the main chain of the polymer, a mercapto group of a side chain or a terminal. Specific examples of the rubber containing a sulfur atom include polysulfide rubber, polyether rubber, polyacrylate rubber, and silicone rubber containing a mercapto group, sulfide bond or disulfide bond. In particular, polysulfide rubber, polyether rubber, polyacrylate rubber, and silicone rubber containing a mercapto group are preferable. In addition, a resin in which a sulfur-containing compound such as pentaerythritol tetrakis (S-mercaptobutyrate), trimethylolpropane tris (S-mercaptobutyrate), or a mercapto group-containing silicone oil is used in a rubber having no sulfur atom is used. You can also. As a commercially available product that can be used as a rubber containing a sulfur atom, “Thicol (registered trademark) LP” manufactured by Toray Fine Chemical Co., Ltd., which is a liquid polysulfide rubber, is preferable. As for content of the sulfur atom in the rubber | gum containing a sulfur atom, 10-30 mass% is preferable.

  The rubber containing a nitrile group is not particularly limited as long as it is a rubber or elastomer containing a nitrile group, but acrylonitrile butadiene copolymer rubber which is a copolymer of butadiene and acrylonitrile is preferably exemplified. As a commercially available product that can be used as a rubber containing a nitrile group, “Nipol (registered trademark) 1042” manufactured by ZEON CORPORATION is preferably exemplified. The amount of nitrile groups in the rubber containing nitrile groups (particularly, the amount of acrylonitrile in the acrylonitrile butadiene copolymer rubber) is preferably 18 to 50% by mass, and more preferably 28 to 41% by mass. When the amount of bound acrylonitrile in the acrylonitrile butadiene copolymer rubber is large, the affinity with metals increases, but the rubber elasticity contributing to stretchability decreases conversely.

  The resin forming the conductive layer is preferably composed only of a rubber containing a sulfur atom and a rubber containing a nitrile group, but within a range that does not impair the conductivity, stretchability, applicability at the time of forming the conductive layer, and the like. In addition, a resin other than a rubber containing a sulfur atom and a rubber containing a nitrile group may be contained. When other resins are also included, the total amount of rubber containing sulfur atoms and rubber containing nitrile groups is preferably 95% by mass or more, more preferably 98% by mass or more, More preferably, the content is 99% by mass or more.

  The amount of the resin occupying the conductive layer (in other words, the amount of the resin solid occupying in the total solid content of the conductive paste for forming the conductive layer) is preferably 55 to 85% by volume, more preferably 60 to 80%. % By volume. When the amount of the resin is too small, the conductivity is increased, but the stretchability tends to be deteriorated. On the other hand, when the amount of the resin is too large, the stretchability is improved, but the conductivity tends to decrease.

  The conductive layer in the present invention is formed by coating or printing a composition (conductive paste) obtained by dissolving or dispersing the above components in an appropriate organic solvent directly on the first insulating layer in a desired pattern. Then, the organic solvent contained in the coating film is volatilized and dried to form. Alternatively, the conductive paste is applied or printed on a release sheet or the like to form a coating film, and then the organic solvent contained in the coating film is volatilized and dried to form a sheet-like conductive layer in advance. Alternatively, it may be laminated on the first insulating layer in a desired pattern.

  The conductive paste can be prepared by appropriately adopting a conventionally known method for dispersing powder in a liquid and uniformly dispersing the conductive filler in the resin. For example, after mixing a metal powder, a dispersion of a conductive material, and a resin solution, they may be uniformly dispersed by an ultrasonic method, a mixer method, a three-roll mill method, a ball mill method, or the like. These means can be used in combination.

  The method for applying or printing the conductive paste is not particularly limited. For example, the coating method, the screen printing method, the lithographic offset printing method, the ink jet method, the flexographic printing method, the gravure printing method, the gravure offset printing method, the stamping method, the dispensing And printing methods such as squeegee printing can be employed.

  In order to volatilize and dry the organic solvent after forming the coating film with the conductive paste, for example, heating may be performed in the air, in a vacuum atmosphere, in an inert gas atmosphere, or in a reducing gas atmosphere. The heating temperature may be selected, for example, in the range of 20 to 200 ° C. in consideration of required conductivity, heat resistance of the base material and the insulating layer, and the like.

150-30 micrometers is preferable and, as for the dry film thickness of a conductive layer, More preferably, it is 100-50 micrometers. If the conductive layer is too thin, it is likely to deteriorate due to repeated expansion and contraction of the electrode and the wiring sheet, and the conduction may be hindered or cut off. On the other hand, if it is too thick, the elasticity of the base material is inhibited and the entire thickness of the electrode and the wiring May become thick and may interfere with comfort.

(Second insulation layer)
The wiring sheet used in the present invention preferably has a second insulating layer formed on the conductive layer. This prevents moisture such as rain and sweat from touching the conductive layer when the biological information measuring interface manufactured using the stretchable wiring sheet is worn.

  As resin which forms a 2nd insulating layer, the thing similar to resin which forms the 1st insulating layer mentioned above is mentioned, A preferable resin is also the same. Only one type of resin forming the second insulating layer may be used, or two or more types may be used. The resin that forms the first insulating layer and the resin that forms the second insulating layer may be the same or different, but it is the same that the coverage of the conductive layer and the wiring sheet are the same. This is preferable from the viewpoint of reducing the damage to the conductive layer due to the uneven stress during expansion and contraction. As described above, the second insulating layer can be formed in the same manner as the first insulating layer. Moreover, a commercially available sheet | seat thru | or film which has the appropriate physical property to carry out after surgery can also be used.

  The film thickness of the second insulating layer is preferably 200 to 20 μm, more preferably 150 to 20 μm. If the second insulating layer is too thin, the insulating effect tends to be insufficient due to repeated expansion and contraction of the base material. On the other hand, if it is too thick, the elasticity of the wiring sheet is hindered and the overall thickness of the wiring becomes thick and comfortable. There is a risk of obstruction.

  In a preferred embodiment of the stretchable electrode and wiring sheet used in the present invention, the load per unit width when stretched at a stretch rate of 10% is 100 N / cm or less, more preferably 80 N / cm or less, and even more preferably 50 N / cm. It is as follows. Conventional conductive fabrics and wirings have a load per unit width of 100 N or more when stretched at a stretch rate of 10%, and it is difficult to follow the stretch of the base material, which causes an obstacle to comfort when worn. . On the other hand, the stretchable electrode and the wiring sheet of the present invention are applied at the time of elongation of 10% by using a rubber containing a sulfur atom and / or a rubber containing a nitrile group as a resin for forming a conductive layer. There is a feature that the load per unit width can be suppressed to 100 N / cm or less. The details of the extension-load test in the present invention are described in Examples.

In a preferred embodiment of the stretchable electrode and wiring sheet of the present invention, the change in electrical resistance due to 20% elongation is 5 times or less, more preferably 4 times or less, and even more preferably 3 times or less. Even if the conventional conductive fabric and wiring are usually disconnected at a stage until the elongation rate reaches 20%, or even if the elongation rate can be expanded to 20%, the electrical conductivity decreases significantly as the resistance change magnification exceeds 10 times. Produce. On the other hand, the stretchable electrode and the wiring sheet of the present invention are resistant even when stretched to 20% by using a rubber containing a sulfur atom and / or a rubber containing a nitrile group as a resin for forming a conductive layer. The change rate can be suppressed to 5 times or less. The details of the extension test in the present invention are described in Examples.

  In a preferred embodiment of the stretchable electrode and wiring sheet of the present invention, the thickness is 400 μm or less, more preferably 300 μm or less, and even more preferably 200 μm or less. The thickness of a conventional conductive fabric or wiring is 400 μm or more, and tends to give the wearer a foreign body feeling when touching the skin side. On the other hand, the stretchable electrode and the wiring sheet of the present invention include a conductive filler mainly composed of metal powder, and a conductive layer formed of rubber containing sulfur atoms and / or rubber containing nitrile groups as a resin. Further, it has a feature that the thickness can be suppressed to 400 μm or less while having high conductivity.

  The electrode and wiring sheet of the present invention can be laminated on a substrate such as clothing. It is preferable to laminate the insulating first layer side with respect to the substrate, and the laminating method is not particularly limited as long as it is a conventionally known laminating method such as laminating with an adhesive or laminating by hot pressing. From the viewpoints of fitting to the body when worn for biometric information measurement and followability during exercise and operation, a lamination method that does not hinder the stretchability of the electrode and the wiring sheet is preferable.

(Clothes for measuring biological information)
The biological information measuring garment of the present invention has a structure in which the electrode is laminated on the garment so that the position when worn is the predetermined position, and preferably the wiring sheet is laminated on a base material such as garment. It is. The garment of the present invention is not particularly limited as long as it is a garment made of a belt, a belt-like object such as a bra, and / or a knitted fabric or a non-woven fabric, which is worn at least in the circumferential direction of the trunk of the human body, Conventionally known products made of various resins, and woven or knitted fabrics or nonwoven fabrics composed of natural fibers, synthetic fibers, and semi-synthetic fibers can be used. The form in the case of using a well-known clothing is not specifically limited, Clothing of forms, such as sportswear, a T-shirt, a polo shirt, underwear, a nightclothes, a cutter shirt, a lab coat, can be used. The electrode 1 that contacts at least a part of the region A and the electrode 2 that contacts at least a part of the region B are provided inside the garment, and biological information is measured by wearing them. In order to measure biometric information, those having elasticity are preferable from the viewpoints of fit to the body when worn and followability during exercise and movement. Such a garment for measuring biometric information becomes a means for measuring the biometric information of the wearer, has a normal wearing method and a feeling of wearing, and can easily measure various types of biometric information simply by wearing it.

  The biological information measuring method and the biological information measuring garment of the present invention preferably include means for measuring the biological information of the measurement subject by the electrode and a mechanism for analyzing the measured information. . The electrode and the mechanism for analyzing the measured information are connected by the wiring.

  As a mechanism for analyzing the measured information, a conventionally known analysis device (such as a heart rate monitor, an electrocardiograph, or an electromyograph) according to the purpose may be employed, and includes means for transmitting information to an external analysis device. .

  The biological information measuring method and biological information measuring clothing of the present invention are combined with biological information collected by the biological information measuring method and biological information measuring clothing different from the present invention based on the collected biological information. It can also be applied to techniques for grasping a person's psychological state and physiological state. For example, mental training by measuring the degree of relaxation, prevention of sleep driving by detecting drowsiness, depression or stress diagnosis by measuring an electrocardiogram, and the like.

EXAMPLES Hereinafter, the present invention will be described more specifically with reference to examples. However, the present invention is not limited by the following examples, but may be appropriately modified within a range that can meet the purpose described above and below. Of course, it is possible to implement them, and they are all included in the technical scope of the present invention.
Follow the procedure below to perform a simulation to find electrode position candidates.

(1) Modeling clothing materials,
In this embodiment, knit is selected as the clothing material. A model called Abaqus's Rebar layer is applied to the modeling of clothing materials, and a four-node shell element (type S4R) with a super-elastic constitutive law by neo-Hookean, warp and weft The river corresponding to is combined. As a result, nonlinear and anisotropic characteristics can be expressed in the shell element. As a result of a tensile test on a single-axis test piece (length 50 mm x width 25 mm) cut out from clothes, the warp and weft directions are in good agreement in the test and analysis, and diagonally (bias) The direction was able to match the test and analysis up to about 30% elongation. Since the elongation of the clothes handled in this example was estimated to be about 30% at the maximum, it was determined that the clothes pressure could be properly analyzed with this model.

(2) Modeling sutures and clothes,
General-purpose FEM (Abaqus / Standard 6.14) was used for the analysis. In order to obtain a quasi-static convergent solution for a clothing simulation for a stationary human body, a static analysis was first performed. At this time, an artificial viscosity method was used to analyze local instability phenomena such as wrinkles. In order to investigate the effects of friction, analysis was performed for cases where the friction between the human body and clothes was not taken into account and when it was taken into account (the friction coefficient was μ = 0.8). In this example, two paper pattern models of the front and back of the body of a sports shirt were created, the predetermined positions were stitched, and the collision calculation to the actual situation was performed to obtain the result after wearing on the stationary human body. If friction was not taken into account, slipping always occurred, and the hem turned up, resulting in excessive wrinkles at the waist.However, when the friction coefficient was taken as 0.8, the displacement between the human body and clothes was suppressed, and wrinkles were observed. This model was adopted because it was confirmed that there was no occurrence of the problem. It was confirmed separately that the average value of the coefficient of friction between the human body and clothes was about 0.8 on average.

(3) Analysis of human body data,
As a human body model, an average human body size mannequin WD-20 (made by Nanai Co., Ltd.) of Japanese women in their 20s was adopted, and the shape of the mannequin was measured three-dimensionally and modeled as a rigid body. In this embodiment, the mannequin model is used to model a moving human body as simply as possible. In this embodiment, data obtained by actually measuring the motion of the jogging human body by motion capture is prepared, the amount of movement of each part of the body is obtained, and the human body in the motion state is corrected by the method of correcting the three-dimensional shape of the mannequin. The shape was modeled. The software used was Maya (R) and MotionBuilder (R) from Autodesk.

(4) Clothing simulation,
The clothing pressure was analyzed by an implicit motion analysis in Abaqus / Standard 6.14 using the modeling method of the human body shape in the motion state and using the model considering the posture change of the human body during jogging. When using T-shirt paper pattern A with a generous amount of space, no wrinkle was observed during clothing, but when waking up, a wrinkle of clothing occurred on the right waist, and as the posture changed thereafter As a result, wrinkles repeatedly moved left and right. It was determined that stable electrocardiogram measurement was difficult even at the part that was in fixed contact with the human body surface at rest, as it was understood that the body surface slipped and moved with the change of posture after the start of exercise.

In view of the above results, the T-shirt pattern B was changed to a relatively tight T-shirt pattern B, and the same examination was performed. The present inventors have grasped from the results of past sensory tests on clothing pressure that the upper limit of clothing pressure that does not impair comfort is about 2 kPa. Furthermore, the sensitivity of tightening varies depending on the body part, and it is desirable that there is a clearance at the upper part of the trunk from the shoulder to the chest, but the sensitivity to tightening is relatively lower at the lower part of the trunk centering on the waist. I know it ’s low. The T-shirt paper pattern B used was a paper pattern with a slightly narrowed waist as illustrated in FIG. As a result of calculation using this pattern paper data, it was found that the maximum clothing pressure at rest is about 1 kPa or less. The obtained results are shown in FIG. Shown in When T-shirt paper pattern A was used, wrinkles generated on the back were almost eliminated, and the result was that the T-shirt was almost in contact with the human body surface. In the back and left armpits, it was confirmed that the state of sticking to the surface of the human body without slipping continued during the exercise. This part of the mannequin model has a large curvature on the surface of the human body, so it is easy to maintain the contact surface pressure, and it was predicted by simulation that it would be suitable as the position of the detection end electrode for electrocardiogram measurement.

In order to examine the back and left armpit area where a relatively stable clothing pressure was obtained in more detail, the time-dependent change in clothing pressure at each position (1) to (8) shown in Fig. 1 was obtained. It was. The results are shown in FIG. Shown in Furthermore, the result of having graphed each position independently is shown in FIGS. The result in the unstable state at the beginning of the exercise was omitted.
Table 3. Maximum clothing pressure, minimum clothing pressure, arithmetic mean clothing pressure, and variation in the range from 10 seconds to 200 seconds after the start of exercise at each position. Shown in (4) The positions of (5) and (6) satisfy the conditions that the arithmetic average clothing pressure is 0.5 kPa or more, the minimum clothing pressure is 0.6 kPa or more, and the variation is 60% or less. .
This position is between the posterior axillary line on the left side surface of the human body and the line (line 1) parallel to the posterior axillary line located at a position on the human body surface at a distance of 10 cm away from the back side of the human body. The region of the human body that satisfies the position and the vertical position between the upper end of the seventh rib and the lower end of the ninth rib (region A), and the rear axillary line on the right side surface of the human body and the rear axillary line at a distance of 10 cm The region of the human body surface that satisfies the left and right positions between the posterior axillary line and the line parallel to the line (line 2) located at the position of the human body surface that is far away from each other, and the vertical position between the upper end of the seventh rib and the lower end of the ninth rib ( This corresponds to region B).

Insulating layer forming resins and conductive pastes used in the following examples and comparative examples were prepared as follows.
(Conductive paste)
The resin shown in Table 1 is dissolved in diethylene glycol monomethyl ether acetate, and silver particles ("aggregated silver powder G-35" manufactured by DOWA Electronics Co., Ltd., average particle diameter of 5.9 μm) are added to this solution, and a method described later as necessary. A liquid in which the surface-treated carbon nanotubes (CNT) prepared in the above were uniformly dispersed was added so that each component had the composition shown in Table 1, and kneaded with a three-roll mill to obtain a conductive paste.

The details of the resin shown in Table 1 are as follows.
Nitrile group-containing rubber: “Nipol (registered trademark) 1042” manufactured by Nippon Zeon Co., Ltd. (acrylonitrile content: 33.3% by mass)
・ Sulfur-containing rubber: “Thiocol (registered trademark) LP-23” manufactured by Toray Fine Chemical Co., Ltd. (sulfur content 21.5 mass%)
・ Polyester: "Byron (registered trademark) RV630" manufactured by Toyobo Co., Ltd.

Moreover, the surface treatment carbon nanotube (CNT) was produced by the following method.
(Production of CNTs having acrylonitrile butadiene oligomer on the surface)
50 mg of multi-walled carbon nanotubes (SWeNT MW100, manufactured by Southwest Nano Technologies, diameter 6-9 nm, length 5 μm, aspect ratio 556-833) was added to 100 mL ethanol solution of 0.006 mol / L o-phenylphenylglycidyl ether. The sonication was performed for 30 minutes. After filtration using a PTFE membrane, washing with ethanol several times, and drying, carbon nanotubes having glycidyl groups on the surface were produced.

  Next, this carbon nanotube was added to a tetrahydrofuran solution of Hypro ™ 1300 × 16ATBN (acrylonitrile content 18% by mass, amine equivalent 900, manufactured by Emerald Performance Materials), which is a terminal amino group acrylonitrile butadiene oligomer, and an ultrasonic treatment machine. For 30 minutes. Furthermore, after heating to 60 ° C. and performing ultrasonic treatment for 1 hour, it was filtered using a PTFE membrane, washed several times with tetrahydrofuran, and then dried to obtain carbon nanotubes having acrylonitrile butadiene oligomer on the surface.

The details of the polyurethane sheet shown in Table 1 are as follows.
-Polyurethane sheet with hot melt: Nisshinbo "Mobilon (registered trademark) MF-10F3"
Polyurethane hot melt sheet: “Mobilon (registered trademark) MOB100” manufactured by Nisshinbo Co., Ltd.

(Production Examples 1-4)
The conductive paste prepared with the formulation shown in Table 1 was applied onto a release sheet, and dried in a hot air drying oven at 120 ° C. for 30 minutes or more to prepare a sheet-like conductive layer with a release sheet. The following polyurethane sheets were laminated using a hot press machine under the conditions of a pressure of 0.5 kg / cm ² , a temperature of 130 ° C., and a press time of 20 seconds.

(Production Examples 1 and 3)
Next, after pasting the polyurethane hot melt sheet shown in Table 1 on the conductive sheet with a release sheet, the release film was peeled off to obtain a conductive sheet with polyurethane hot melt. Thereafter, the polyurethane sheet with hot melt shown in Table 1 is bonded to a region having a length of 19 cm and a width of 2 cm, and a conductive sheet with polyurethane hot melt having a length of 19 cm and a width of 1 cm is bonded to the first insulating layer and the conductive layer. Formed parts with. Next, a 2-way tricot fabric having a length of 19 cm and a width of 5 cm (“KNZ2740” manufactured by Gunsen Co., Ltd., nylon yarn: urethane yarn = 63%: 37% (mixing ratio), basis weight 194 g / m ² ) Parts having an insulating layer and a conductive layer were laminated to obtain a stretchable electrode sheet.

(Production Examples 2 and 4)
Next, by laminating the same hot melt-coated polyurethane sheet as that in which the first insulating layer is formed in a region having a length of 17 cm and a width of 2 cm so as to cover the part including the first insulating layer and the conductive layer formed above. A second insulating layer was formed on the conductive layer to obtain a stretchable wiring sheet having a configuration of first insulating layer / conductive layer / second insulating layer.

The stretchable electrode and wiring sheet obtained in each production example were subjected to the following tests and evaluated.
<Extension-load test>
Tensilon ("RTM-250" manufactured by ORIENTEC CORPORATION) was used to stretch a stretchable electrode and wiring sheet with a fabric width of 5 cm, electrode and wiring width of 2 cm, chuck length of 6 cm, and test length of 5 cm at a stretch rate of 100%. The load (N / cm) per unit width of the electrode and wiring when 10% elongation (displacement amount 0.5 cm) was measured.
<Electrical resistance measurement>
In the above-described elongation-load test, the resistance between the stretchable electrode and the conductive layer of the wiring sheet was measured using a digital multimeter (“YOKOGAWA TY530” manufactured by Yokogawa Meter & Instruments) for an initial measurement distance of 17 cm. The change in resistance (Ω) due to the value (Ω) and elongation was measured.
<Extension test>
Using an elongation tester (hand-drawing stretcher) equipped with two chucks with a width of 2.5 cm, the stretchable electrode and the wiring sheet are sandwiched at a distance of 5 cm between the chucks, and stretched to a stretch rate of 20% in the longitudinal direction (displacement 1 cm) )did. The electrical resistance before and after the test was measured using a digital multimeter (Yokogawa Meter & Instruments "YOKOGAWA TY530"), and the resistance value (Ω) was measured outside the two opposing chucks (measurement distance 10 cm). The resistance value was measured immediately after extension (within 3 seconds).

<Resistance change magnification>
The resistance change magnification is the ratio of the resistance value (R ₂₀ ) when the elongation rate is 20% to the resistance value (R ₀ ) when the elongation rate is 0% (before the test) (that is, the resistance change magnification = R ₂₀ / R). ₀ (times)).

<Electrocardiogram measurement method and SN ratio calculation method>
The shirts equipped with the electrodes of Examples and Comparative Examples were worn and rested for 20 minutes in a room at 25 ° C. and 50% RH, and then an electrocardiogram at rest for 12 minutes was measured. Next, an electrocardiogram during walking for 12 minutes was measured with a treadmill set to 2.7 km / h. The dispersion of the amplitude of the R wave from the waveform of the electrocardiogram for 10 minutes excluding the first minute and the last minute during rest and walking is used as the signal (S), and the amplitude of the waveform between the R wave and the R wave The S / N ratio was determined by the equation of S / N with the variance as noise (N).
Females whose body dimensions were within the average human body size mannequin WD-20 (manufactured by Nanasai Co., Ltd.) of Japanese women in their 20s used in the simulation and within ± 5% were used as subjects.

(Electrode wiring example 1)
In production examples 1 and 2, the first insulating layer having a 5 cm × 5 cm square and a wiring width of 1 cm is formed by forming a conductive layer with a release layer and then cutting the sample into a predetermined size and shape to change the sample size. A sample was prepared in which a stretchable electrode having a structure of / conductive layer and a stretchable electrode having a structure of first insulating layer / conductive layer / second insulating layer were integrated.

(Electrode wiring example 2)
In Production Examples 3 and 4, the first insulating layer having a 5 cm × 5 cm square and a wiring width of 1 cm is formed by forming a conductive layer with a release layer and then cutting the sample into a predetermined size and shape to change the sample size. A sample was prepared in which a stretchable electrode having a structure of / conductive layer and a stretchable electrode having a structure of first insulating layer / conductive layer / second insulating layer were integrated.

(Examples 1 to 3, Comparative Example 1)
The clothing which affixed the electrode wiring examples 1 and 2 to the position described in Table 2 on the back side of the shirt was prepared, the electrode surface roughness was measured, and the subject wore the clothing and the electrocardiogram was measured. In addition, the outline of the shape of the clothing which affixed the electrode wiring of Examples 1-3 is as FIG.

  As a result of the electrocardiogram measurement, Examples 1 to 3 in which electrodes are provided at two positions, a position in contact with the region A and a position in contact with the region B, have little noise during measurement and good SN ratio when resting and walking. Thus, an electrocardiogram waveform capable of easily detecting the R wave could be obtained. In Comparative Example 1 in which the electrode was provided at a position not in contact with the region A, the SN ratio at rest was good, but the contact between the electrode and the living body surface was bad due to the movement of the scapula during walking, and noise during measurement was In many cases, the S / N ratio was poor, detection of R waves was difficult, and correct biological information could not be obtained.

The present invention provides a biological information measurement method and a biological information measurement garment that can be measured even during a walking motion or an exercise motion such as running, and is suitably used in the health monitoring field, the medical field, and the like. It is what is done.
Further, here, for convenience, the “human body” is mainly handled, and the technical disclosure has been made on the preferred electrode positions particularly for acquiring electrocardiographic data. However, when the collection target is a myoelectric potential or the like at a specific body position, What is necessary is just to arrange | position the signal detection end and electrode for the target data collection in the place where appropriate clothing pressure is obtained using a system. By using the present invention, it is possible to provide a biological signal measurement garment that fits an arm, a foot, fingers, a neck, a face, and a trunk.
In addition, the target to which the system of the present invention can be applied is not necessarily limited to humans, and can be applied to animals living on land widely. The present invention can be applied to collection of biological information of auxiliary animals such as pets, domestic animals, guide dogs, service dogs, and hearing dogs. In addition, it can be applied to observation of wild animals in combination with GPS that provides position information.

9 ... Electrode 10 ... Wiring

Claims (6)

Sensing wear having a detection end in contact with the body surface on the inside of the clothes,
(1) Modeling clothing materials,
(2) Modeling sutures and clothes,
(3) Analysis of human body data,
(4) Sensing ware having a detection end where a pressure due to clothing pressure found by performing clothing simulation is stably generated. The sensing wear according to claim 1, wherein the detection end is disposed at a location where the clothing pressure is 0.5 kPa or more. 3. The sensing ware according to claim 1, wherein the detection end is arranged at a location where the variation in clothing pressure from 10 seconds after the start of exercise to 200 seconds is within 60% by the clothing simulation. The sensing wear according to any one of claims 1 to 3, wherein the detection end is a skin contact electrode, and the area of the skin contact electrode is 1 cm ² or more.   The sensing ware according to any one of claims 1 to 4, wherein the biological information to be measured is an electrocardiogram including at least an R wave.   The sensing wear according to any one of claims 1 to 5, wherein the skin contact electrode includes a wiring, and the electrode and the wiring are made of the same material.