JP2011015817A - Fabric with multiple electrode - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a fabric with multiple electrodes which are useful as electrodes for easily and precisely measuring bioelectric signals such as a cardiac potential signal without restraining a subject even in measurement for a long period of time and affecting an affected area such as a skin, and clothes for measuring bioelectric signals using it.SOLUTION: The fabric with multiple electrodes includes a conductive region and a nonconductive region formed by tapestry-weaving conductive yarn and nonconductive yarn and has a plurality of the electrodes comprising the conductive region.

Description

  The present invention relates to a fabric with multiple electrodes and a garment for measuring a bioelectric signal using the same.

  Typical examples of the bioelectric signal are an electrocardiogram signal and a myoelectric signal, and the biofunction is examined by measuring them.

  For example, general electrocardiogram recording for measuring an electrocardiographic signal is for measuring cardiac function at rest, and is performed by an electrocardiogram that records changes in voltage generated on the body surface of a subject. For the electrocardiogram measurement, the electrode is fixed by adhering it to the skin with an adhesive near the wrist or ankle of the subject, or by adsorbing it to the body surface such as the chest using reduced pressure. A cardiac potential signal obtained from the electrodes was amplified by an amplifier, recorded on a recorder, and displayed on a display screen. During the measurement, the subject is usually required to rest on his back on the examination table. The electrode is fixed to the subject every time it is measured, and it is fixed to the body surface by using an adhesive or depressurizing as described above. It is difficult to measure without.

  In general, six electrodes are adsorbed on the chest, V1 is the right edge of the fourth intercostal sternum, V2 is the left edge of the fourth intercostal sternum, V4 is on the left intercostal line of the fifth intercostal space, and V3. Is mounted at the midpoint of V2 and V4, V5 is mounted on the anterior axilla line at the same height as V4, and V6 is mounted on the midaxillary line at the same height as V4. Since the rib cage has an uneven structure in which the ribs and ribs appear alternately, depending on the body shape and the state of the body surface, the adsorption may not be successful, and the electrodes often come off. In addition, it is necessary to pay attention so as to quickly mount the electrodes in the correct positions without making a mistake in the order of the electrodes. Furthermore, with six electrodes, it is difficult to sufficiently estimate the potential distribution on the body surface generated from the heart, and there is a limit to accurately grasping the state of cardiac function.

  On the other hand, if you have paroxysmal, isolated, or transient heart disease, it is difficult to grasp cardiac function with a short ECG recording. Intentionally, for example, it is necessary to record a long-time electrocardiogram with a Holter electrocardiograph (long-term electrocardiograph). However, even in this case, the subject is required to have the electrode attached, the behavior is restricted when the electrode is attached, and the skin contact surface to which the electrode is attached causes itching, redness, inflammation, etc. Sometimes it happened. In addition, since the subject himself cannot easily attach and detach, it is difficult to measure a part of daily activities such as bathing. Therefore, the measurement can be performed only for about 24 hours, and the abnormality occurs once every few days. It has been considered impossible to obtain an electrocardiogram.

  Similarly, it can be worn continuously for a long time, or it can be worn during a specific job to continuously measure signals obtained from the living body itself, receive signals generated from devices existing inside the living body, or On the contrary, there are many cases where it is necessary to provide a signal to the living body itself or to a device existing inside the living body. For example, when measuring sweating and body surface temperature for firefighters and other persons engaged in special activities, many measurement electrodes and sensors are attached to the body surface when they are dispatched. It is not preferable to perform the wiring work for tying to the wiring because it is a waste of time, and it is necessary to provide a method for arranging the measuring electrode group that is electrically tied in a short time on the body surface. In addition, for example, when using a capsule endoscope or an implantable blood test / treatment device under research proposal, a group of receivers that receive signals from these devices and wiring that electrically connects them are displayed on the body surface. If it cannot be easily attached to and detached from the appropriate site, it is impossible to continuously measure without disturbing daily life. In addition, for example, in order to continuously use devices such as cochlear implants, cardiac pacemakers, or electrical function stimulators that improve the function of the human body by directly stimulating the brain and muscles in daily life, If the electrical circuit for providing power and commands to these devices from the outside, the transmitter / receiver, and the wiring that electrically connects them can not be easily attached to and detached from appropriate parts of the body surface, it will interfere with daily life It is difficult to maintain the function of the device continuously without any problems.

  The present invention has been made in view of the above circumstances and problems, and does not constrain the subject's daily behavior and does not affect the skin or the like, even with long-term measurement. An object of the present invention is to provide a fabric with multiple electrodes useful as an electrode that can easily and accurately measure a bioelectric signal such as an electrocardiographic signal by attaching and detaching an electrode, and a bioelectric signal measurement garment using the fabric. And

  The present invention is (1) a multi-electrode comprising a plurality of electrodes composed of a conductive region by forming a conductive region and a non-conductive region by binding and weaving a conductive yarn and a non-conductive yarn. It relates to a woven fabric.

  Further, the present invention is (2) a multi-electrode woven fabric as described in (1) above, wherein the non-conductive yarn is used for either warp or weft and the conductive yarn is used for the other. About.

  In the present invention, (3) the plurality of electrodes are spaced apart from each other and are electrically insulated by a non-conductive region, according to (1) or (2), The present invention relates to a fabric with multiple electrodes.

  In the present invention, (4) any one of the above (1) to (3), wherein a conductive portion formed by extending a conductive yarn forming the electrode is formed from the electrode. The woven fabric with multiple electrodes according to one item.

  The present invention also relates to (5) the multi-electrode fabric according to (4), wherein the conductive portion is covered with an insulator.

  The present invention also relates to (6) a bioelectric signal measurement garment produced using the multi-electrode-attached fabric according to any one of (1) to (5).

  The present invention also relates to (7) the bioelectric signal measurement garment according to (6), wherein the bioelectric signal is a myoelectric signal or a cardiac potential signal.

  According to the present invention, since it can be easily attached and detached by the subject's own hand, even in the measurement over a long period of time, without restricting the daily behavior of the subject, without affecting the skin, It is possible to provide a fabric with a multi-electrode useful as an electrode that can easily and accurately measure a bioelectric signal such as an electrocardiographic signal and a garment for measuring a bioelectric signal using the same.

It is a schematic diagram of the fabric with multiple electrodes of the present invention. It is a schematic diagram of the fabric with multiple electrodes of the present invention. It is a schematic diagram of the electrode in the fabric with multiple electrodes of the present invention. It is a schematic diagram of the electrode in the fabric with multiple electrodes of the present invention. It is a schematic diagram of the electrode in the fabric with multiple electrodes of the present invention. It is a schematic diagram of the electrode in the textile fabric with multiple electrodes of this invention. It is a schematic diagram of the electrode in the textile fabric with a multielectrode of this invention produced in the Example. It is the electrocardiogram measured using the textile fabric with a multielectrode of this invention produced in the Example.

  The woven fabric with multiple electrodes of the present invention is formed by forming a conductive region and a non-conductive region by binding and weaving a conductive yarn and a non-conductive yarn, and includes a plurality of electrodes made of the conductive region. It is characterized by that.

  The present invention will be described below with reference to the drawings.

  The fabric 1 with multiple electrodes of the present invention comprises a plurality of electrodes, and even if the plurality of electrodes are arranged on the entire fabric as shown in FIG. As shown in b), it may be arranged in part. For example, when measuring a bioelectric signal using a multi-electrode fabric in which a plurality of electrodes are provided on the entire fabric, depending on the type of bioelectric signal to be measured, the measurement site, the body shape of the subject, etc. These electrodes may be arbitrarily selected as measurement electrodes. In addition, when measuring a bioelectric signal using a multi-electrode woven fabric in which a plurality of electrodes are provided in a part of the woven fabric, for example, a clothing design may be designed so that the electrodes are arranged at the measurement site. .

  The multi-electrode-attached fabric 1 of the present invention comprises a conductive region A and a non-conductive region B, and the conductive region A constitutes an electrode 2 (see FIGS. 1 and 2). As shown in FIG. 1, the plurality of electrodes 2 are spaced apart from each other, and each electrode 2 is electrically insulated by a non-conductive region B for the purpose of preventing a short circuit between the electrodes 2. It is possible to increase the number of channels when the distance between the electrodes 2 is as short as possible. However, if the distance between the electrodes is too short, the signal amplitude of the bioelectric signal is reduced and the S / N ratio is lowered, making signal detection and signal analysis difficult. Therefore, it is necessary to appropriately set the electrode interval according to the measurement conditions. There is. The arrangement of the electrodes 2 is not particularly limited, and may be evenly spaced as shown in FIG. 1 or may be unevenly spaced.

  The conductive region A and the nonconductive region B are formed by binding and weaving the conductive yarn 3 and the nonconductive yarn 4 as shown in FIG. In the present invention, the conductive region A and the non-conductive region B can be suitably formed at desired positions by using a stitch weaving technique. In addition, by using the weaving technique, the conductive part to be woven can be realized using a single continuous thread, so compared to the case where the circuit shape is woven by a plurality of threads coming into contact with each other. The circuit resistance can be reduced to about 1/100. In the weaving technique, when the conductive yarn 3 and the non-conductive yarn 4 are used for the weft as shown in FIG. 3, the conductive yarn 3 which is the weft of the conductive region A does not pass through the entire fabric, and the conductive weave 3 Since the non-conductive region B is woven only by the conductive region A and the non-conductive region B is woven by the non-conductive yarn 4, a gap is formed at the boundary between the weft of the conductive region A and the weft of the non-conductive region B. In addition, since the front and back patterns are the same in the stitch weaving technique, in the woven fabric 1 with multiple electrodes, the conductive region A and the non-conductive region B are formed on the front surface and the back surface. Using the back side of the surface that touches the skin, it is possible to easily join the electric devices, and there is an advantage that the subject can easily check the electrode wearing position.

  In the present invention, non-conductive yarn is used for either the warp or the weft, and the conductive yarn is used for the other. As shown in FIG. 3, the conductive region and the non-conductive region are easily formed accurately and easily at a desired position. As shown in FIG. 3, the non-conductive yarn is used for the warp, and the conductive yarn and the non-conductive yarn is used for the weft. It is preferable to use it. As other embodiments, conductive yarn and non-conductive yarn are used for the warp, non-conductive yarn is used for the weft, or conductive yarn and non-conductive yarn are used for the warp, and conductive yarn and non-conductive yarn are used for the weft. It may be used to carry out spell weaving.

  In the present invention, when weaving and weaving using a non-conductive yarn as the warp and a conductive yarn and a non-conductive yarn as the weft, the weft is woven with a reduction ratio of 3 to 7 with respect to the warp. Then, the slack according to the shrinkage is raised on the warp yarns intersecting to form a spelled woven structure. Since the electrode in the resulting multi-electrode fabric is raised, the bioelectric signal measurement garment made using the fabric is easily attached to the body surface of the subject and easily senses the bioelectric signal. . Here, the reduction ratio is the actual dimension (length L) of the yarn when the yarn woven within a certain dimension (W) of the fabric is taken out of the fabric and measured, and the constant of the fabric. It means the ratio (L / W) to the dimension (W).

  The conductive yarn 3 used in the present invention is a yarn composed of conductive fibers, such as metal yarns such as gold, silver, copper, and stainless steel; inorganic fibers such as carbon, titanium, and alumina; polyaniline, polyacetylene, and the like. Conductive ponomer; silver-plated nylon yarn composed of multifilaments that are bundles of silver-plated nylon filaments; filament yarn and spun yarn (twisted yarn) composed of acrylic fiber, nylon fiber, or polyester fiber containing copper sulfide and nickel; These synthetic yarns, synthetic yarns, blended yarns, spun yarns (twisted yarns), etc. can be used. Among these, stainless steel fibers are preferably used because they are sturdy and easy to process, and stainless fibers having a diameter of 40 μm to 240 μm are more preferably used.

The non-conductive yarn 4 used in the present invention is a yarn made of non-conductive fibers, and for example, cotton yarn, silk yarn, acrylic, nylon, polyester yarn and the like can be used. Among these, a polyester yarn is preferably used from the viewpoint of insulation, and a polyester yarn having an electrical resistance value of 1 × 10 ¹³ Ω / cm or more and an official moisture content of 0.4% or less is more preferably used. The thickness of these nonconductive threads 4 is not particularly limited, but is usually in the range of 50 to 1000 denier.

  The combination of the conductive yarn 3 and the nonconductive yarn 4 is not particularly limited, and is appropriately selected within a range where weaving is possible.

  In the present invention, the shape of the electrode 2 is not particularly limited. For example, a rectangle, a square, a circle, an ellipse, other polygons, concentric multiple figures (concentric squares, concentric circles, concentric polygons), etc. FIG. 4 shows a schematic diagram of concentric rectangular electrodes. The electrode 2 shown in FIG. 4 is formed from a conductive region A, and each electrode 2 is spaced apart by a non-conductive region B and is electrically insulated. In FIG. 4, three concentric square electrodes are shown, but the number of multiple figures is not particularly limited.

  In the present invention, as shown in FIG. 5, a conductive portion 5 formed by extending a conductive thread 3 forming the electrode 2 is formed from the electrode 2. Since the bioelectric signal sensed by the electrode 2 is a weak current, it is necessary to amplify the voltage between the electrodes using an amplifier, and the electrode 2 and the amplifier are connected via the conductive portion 5. The conductive portion 5 normally extends from the woven end of the electrode 2. Since the conductive portion 5 is formed of the conductive yarn 3, there is a possibility of causing a short circuit by coming into contact with the electrode when extending over another electrode. As shown, it is preferably covered with an insulator 6. The insulator 6 is not particularly limited as long as it is made of an insulating material. For example, polyester, polypropylene, acrylic, nylon, polyethylene, polystyrene, polyvinyl chloride, polyvinylidene chloride, polyvinyl alcohol, polysulfone, polyacetal , Polyurethane, polyformal, polybutyral, polyamide, polycarbonate, polyvinyl acetate, copolymers of two or more of the above polymers, fluororesin, silicone resin, epoxy resin, and vinyl ester resin can be used. The method for covering the conductive portion 5 with the insulator 6 is not particularly limited, and examples thereof include a method of applying an insulating material to the conductive portion 5 and a method of covering with a part made of an insulating material.

  In the present invention, the size of the electrode 2 is not particularly limited, and is appropriately selected according to the purpose of use and the application site. For example, when the electrocardiogram signal is measured using the multi-electrode fabric of the present invention, if the electrode size is too small, the contact impedance of the site for detecting the electrocardiogram signal increases, and an electrocardiograph or the like is used for detection. It is necessary to devise a method for increasing the input impedance. On the other hand, if it is too large, the variation in the contact area between the electrode and the living tissue will increase, so that the contact impedance will vary, and noise will be mixed into the electrocardiographic signal. Further, the number of the electrodes 2 in the multi-electrode-equipped fabric is not particularly limited as long as it is plural, and is appropriately selected according to the purpose of use and the application site.

  The bioelectric signal measurement garment manufactured using the multi-electrode fabric 1 of the present invention includes a plurality of electrodes 2, so that bioelectric signals such as cardiac potential signals can be detected from a large number of electrodes. Compared with the conventional electrocardiograph using, more precise measurement can be performed.

  The woven fabric with multiple electrodes of the present invention can be produced in a garment for measuring bioelectric signals. The clothes are not particularly limited as long as the electrodes are of a kind that directly contacts the subject's skin when worn by the subject, and examples thereof include shirts, pants, socks, gloves, and hats. Examples of the bioelectric signal include a cardiac potential signal, a myoelectric potential signal, and an electroencephalogram. Depending on the bioelectric signal to be measured, the electrode is arranged at an appropriate site, for example, the chest of the subject if it is a cardiac potential signal, the muscle you want to measure if it is a myoelectric signal, the head if it is an electroencephalogram What is necessary is just to make the design of clothes so that an electrode may be arranged in the clothes. Since the garment for measuring a bioelectric signal of the present invention only needs to be worn, the measurement can be easily performed without restraining the subject and without affecting the affected area such as the skin, as compared with the conventional electrocardiogram measurement. .

  The multi-electrode-equipped fabric of the present invention is not only an electrical signal directly emitted from a living body, but also an individual electrode or electrical characteristics (resistance, etc.) between a plurality of electrodes depending on the phenomenon such as perspiration. The present invention can also be applied to the measurement of phenomena that are captured as changes in the above. In addition, by connecting an appropriate sensor device or end effector device to the electrode, or by combining it electrically or electromagnetically, it is possible to acquire a phenomenon on the surface of the living body or inside the living body, or to affect the living body itself. You may use for. Examples of such connected / coupled devices include, for example, bending angle sensors for body joints, contact pressure sensors at various points on the body surface, sensors for measuring body surface temperature, and microphones for measuring heart sounds and lung sounds. Signals are sent to a biometric device such as an array or a capsule-type endoscope in the body, or a living body implantable blood sugar concentration or cancer marker concentration, or a cochlear implant, heart pacemaker, brain, muscle, organ, etc. An electrical function stimulating device that improves the function by giving it. In addition, for example, clothing-type information devices in which end effectors such as headphones, microphones, and barcode readers are arranged in appropriate parts such as ears, mouths, hands, etc. are realized by applying the technology of the present invention. it can.

Examples Examples of the fabric with multi-electrodes of the present invention are shown below, but the present invention is not limited thereto.

A warp yarn of 150 denier polyester yarn (made by Teijin Fibers Ltd., trade name: Wavelon, electrical resistance: 1 × 10 ¹³ Ω / cm, official moisture content: 0.3%) is used. Four hundred and fifty denier polyester yarn (made by Teijin Fibers Ltd., trade name: Waveron, electrical resistance: 1 × 10 ¹³ Ω / cm, official moisture content: 0.3%) and 160 μm diameter Of stainless steel fibers (made by Nippon Seisen Co., Ltd., trade name: Naslon, 4 twisted stainless steel fibers with a diameter of 40 μm) and weaving them together to form a 5 mm square electrode 2 in 5 mm length and width directions. A multi-electrode fabric 1 having 60 pieces in a size of 20 cm × 30 cm was prepared by arranging them at intervals (see FIG. 7). On the back surface of the fabric with multiple electrodes, the stainless steel fibers were elongated from the woven ends of the electrodes, and the elongated fibers were each coated with polyvinyl chloride. The resistance value of the stainless steel fiber used for the electrode was 36.3 ± 5.4 Ω / cm.

The back surface of the fabric 1 with multi-electrodes produced as described above was placed in contact with the left chest of the subject, and a reference ground electrode was placed on the back facing the left chest. As a reference ground electrode, a warp yarn of 150 denier polyester yarn (manufactured by Teijin Fibers Ltd., trade name: Wavelon, electric resistance: 1 × 10 ¹³ Ω / cm, official moisture content: 0.3%) is 4 Using this twisted yarn, 4 weft yarns of 150 denier polyester yarn (manufactured by Teijin Fibers Ltd., trade name: Waveron, electrical resistance: 1 × 10 ¹³ Ω / cm, official moisture content: 0.3%) A 5cm side of 5cm per side, produced by spelling and weaving this twisted one and 160μm diameter stainless steel fiber (manufactured by Nippon Seisen Co., Ltd., trade name: Naslon, four twisted 40μm diameter stainless steel fiber) A square electrode was used. FIG. 8 shows an electrocardiogram obtained by measuring the cardiac potential in a resting state using two of the electrodes of the multi-electrode fabric 1 and the reference ground electrode.

A conductive region B nonconductive region 1 woven fabric with multiple electrodes 2 electrode 3 conductive yarn 4 nonconductive yarn 5 conductive part 6 insulator

Claims (7)

  A fabric with multiple electrodes, comprising a conductive region and a non-conductive region formed by binding and weaving a conductive yarn and a non-conductive yarn, and comprising a plurality of electrodes made of the conductive region.   2. The fabric with multi-electrode according to claim 1, wherein the warp yarn or the weft yarn is used for non-conductive yarn and the other is made of conductive yarn, and is woven and bound.   The fabric with multiple electrodes according to claim 1 or 2, wherein the plurality of electrodes are arranged apart from each other and electrically insulated by a non-conductive region.   The fabric with a multi-electrode according to any one of claims 1 to 3, wherein a conductive portion formed by extending a conductive yarn forming the electrode is formed from the electrode.   The woven fabric with multiple electrodes according to claim 4, wherein the conductive portion is covered with an insulator.   A bioelectric signal measurement garment produced using the multi-electrode-attached fabric according to any one of claims 1 to 5.   The bioelectric signal measurement garment according to claim 6, wherein the bioelectric signal is a myoelectric potential signal or a cardiac potential signal.

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