JP5487496B2 - Bioelectric signal measurement device - Google Patents

Description

  The present invention relates to a bioelectric signal measurement electrode and a bioelectric signal measurement device including 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.

  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 bioelectric signal measuring electrode capable of easily attaching and detaching an electrode and measuring a bioelectric signal such as an electrocardiographic signal easily and precisely, and a bioelectric signal measuring device including the same. To do.

  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. The present invention relates to a bioelectric signal measuring electrode using a woven fabric.

  The bioelectric signal measurement according to the above (1), wherein the present invention is (2) binding and weaving using a non-conductive yarn for one of the warp and the weft and a conductive yarn for the other. The present invention relates to an electrode.

  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 bioelectric signal measurement electrode.

  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 bioelectric signal measurement electrode according to one item.

  The present invention also relates to (5) the bioelectric signal measurement electrode according to (4), wherein the conductive portion is covered with an insulator.

  The present invention also relates to (6) a bioelectric signal measurement device comprising the bioelectric signal measurement electrode according to any one of (1) to (5).

In the present invention, (7) a conductive region and a non-conductive region are formed by binding and weaving a conductive yarn and a non-conductive yarn, and a plurality of electrodes comprising the conductive region are provided. A bioelectric signal measuring electrode using a fabric with multiple electrodes;
An amplifier that amplifies the electrical signal detected by the biological signal measurement electrode and generates an amplified signal;
The present invention relates to a bioelectric signal measurement device comprising: a recorder that records a bioelectric signal based on the amplified signal.

  The present invention further includes (8) a conductive portion that connects the bioelectric signal measurement electrode and the amplifier, and the conductive portion is formed by extending a conductive thread that forms the bioelectric signal measurement electrode. The bioelectric signal measurement device according to (7), wherein

  The present invention also relates to (9) the bioelectric signal measurement device according to any one of (6) to (8), wherein the bioelectric signal is a myoelectric signal or a cardiac potential signal.

  In addition, the present invention provides (10) the bioelectric signal measurement electrode according to any one of (6) to (9), wherein the bioelectric signal measurement electrode is used as a multipoint measurement electrode. Relates to the device.

  The present invention also relates to (11) the bioelectric signal measurement device according to any one of (6) to (9), wherein the bioelectric signal measurement electrode is used as a chest induction electrode. .

  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 bioelectric signal measuring electrode capable of easily and precisely measuring a bioelectric signal such as an electrocardiographic signal, and a bioelectric signal measuring device including the same. That is, according to the present invention, the subject himself / herself can easily attach and detach the bioelectric signal measurement electrode and measure the bioelectric signal at the correct position, which can be used for measurement in a long-term daily life. Signs and symptoms of heart disease do not occur so often, and normal Horta electrocardiographs may not be able to measure the signs and symptoms, so it is very possible to measure in daily life for a long time Is meaningful.

It is a schematic diagram of the textile fabric with a multi-electrode used for the electrode for bioelectric signal measurement of this invention. It is a schematic diagram of the textile fabric with a multi-electrode used for the electrode for bioelectric signal measurement of this invention. It is a schematic diagram of the electrode in the textile fabric with multiple electrodes. It is a schematic diagram of the electrode in the textile fabric with multiple electrodes. It is a schematic diagram of the electrode in the textile fabric with multiple electrodes. It is a schematic diagram of the electrode in the textile fabric with multiple electrodes. It is a schematic diagram of the bioelectric signal measuring device of the present invention. It is a schematic diagram of the electrode for bioelectric signal measurement of this invention produced in the Example. It is the electrocardiogram measured using the bioelectric signal measuring electrode of the present invention produced in the example.

  The bioelectric signal measurement electrode according to the present invention includes a plurality of electrodes composed of the conductive regions by forming a conductive region and a nonconductive region by binding and weaving a conductive yarn and a nonconductive yarn. It is characterized by using the fabric with multiple electrodes.

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

  The multi-electrode-equipped fabric 1 used for the bioelectric signal measuring electrode of the present invention comprises a plurality of electrodes, and the plurality of electrodes are arranged on the entire fabric as shown in FIG. Even if it is, it may be arranged in part as shown in FIG. For example, when measuring a bioelectric signal with a bioelectric signal measuring electrode using a multi-electrode fabric in which a plurality of electrodes are provided on the entire fabric, the type of bioelectric signal to be measured, the measurement site, and the body shape of the subject Depending on the above, some electrodes may be arbitrarily selected as measurement electrodes. Further, when measuring a bioelectric signal by a bioelectric signal measuring electrode using a multi-electrode woven fabric in which a plurality of electrodes are provided in a part of the woven fabric, for example, clothing is arranged so that the electrodes are arranged at the measurement site. You can design the design.

  The fabric 1 with multiple electrodes includes 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. In the woven fabric 1 with multiple electrodes, the conductive region A and the non-conductive region B are formed on the same surface on the front surface and the back surface. This makes it possible for the subject to easily check the electrode wearing position.

  In the present invention, the 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 consisting of multifilaments which are bundles of silver-plated nylon filaments; filament yarn and spun yarn (twisted yarn) consisting 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 yarns 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. Among the above shapes, concentric multiple figures are preferable.

  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 an electrocardiogram signal is measured with a bioelectric signal measuring electrode using a fabric with multiple electrodes, if the electrode size is too small, the contact impedance of the part detecting the electrocardiogram signal increases, A device for increasing the input impedance of an electric meter or the like is required. 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. In general, the area of the electrode is preferably ¼ cm ² or more.
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. For example, when measuring an electrocardiographic signal with a bioelectric signal measuring electrode using a fabric with multiple electrodes, the number of electrodes 2 is measured from the viewpoint of obtaining accurate data by measuring the electrocardiographic signal at multiple points. Although it depends on the planned number of inductions, it is preferable that the electrodes are densely arranged around the measurement target point when it is assumed that the difference in physical condition or individual difference of the measurement target individual is absorbed. For example, in the case of electrocardiogram measurement, most ideally, in the region covering the entire heart, i.e., the entire region from the human midline to the left lower arm or the left back, for example, concentric circular electrodes, It is preferable that a plurality of electrodes are arranged with a width of about 7 mm and an interval of about 2 mm between each electrode. If the distance between the electrodes is too narrow, the influence between adjacent electrodes cannot be eliminated, which is not preferable. In addition to the measurement electrodes, the ground electrode is preferably arranged at a point as far as possible from these measurement electrodes.

  Since the bioelectric signal measuring electrode of the present invention includes a plurality of electrodes 2 and can detect a bioelectric signal, for example, an electrocardiographic signal, from a large number of electrodes, compared to a conventional electrocardiograph using six electrodes. It is possible to perform more precise measurement and is useful as a component of a bioelectric signal measuring device.

  The bioelectric signal measurement device of the present invention comprises the bioelectric signal measurement electrode. More specifically, the bioelectric signal measurement electrode, an amplifier that amplifies the electric signal detected by the biosignal measurement electrode and generates an amplified signal, and records the bioelectric signal based on the amplified signal And a recorder. As an example, as shown in FIG. 7, the bioelectric signal measurement device 7 amplifies the clothes 8 having the bioelectric signal measurement electrode C and the electric signal detected by the bioelectric signal measurement electrode C. An amplifier 9 for generating an amplified signal and a recorder 10 for recording a bioelectric signal based on the amplified signal are provided.

  The bioelectric signal measuring electrode C of the present invention can be manufactured on the garment 8 because it uses a fabric with multiple electrodes. 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 bioelectric signal measurement electrode C is disposed at an appropriate site, for example, the chest of the subject if it is a cardiac potential signal, the muscle to be measured if it is a myoelectric signal, In the case of an electroencephalogram, a clothing design may be prepared so that electrodes are arranged on the head. Since the subject only needs to wear it by making it into clothes, the subject can be easily measured for a long time without restraining the subject and without affecting the skin or the like, as compared with the conventional electrocardiogram measurement.

  The amplifier 9 is electrically connected to the bioelectric signal measurement electrode C by the conductive portion 11 and is not shown in the drawing, but the amplifier 9 is an analog / digital converter, a microcontroller, a battery, etc. It can be carried by being fixed to the subject by a belt or the like (not shown). The conductive portion 11 is formed by extending a conductive yarn forming the electrode 2 in the bioelectric signal measuring electrode C, and the conductive yarn is covered with an insulator for the purpose of preventing a short circuit. Is preferred.

  As long as the recorder 10 records a bioelectric signal based on an amplified signal, the recorder 10 wirelessly transmits and receives the amplified signal even if it is electrically connected by the amplifier 9 and the conductive portion 11. It may be. In addition, even when bioelectric signals are recorded on recording paper in real time, bioelectric signal data is recorded on an appropriate recording medium such as a memory and then printed in a lump. It may be.

  Such a configuration of the recorder 10 is appropriately set according to a usage pattern of the bioelectric signal measurement device 7. For example, when the bioelectric signal of an inpatient is measured by the bioelectric signal measurement device 7. If so, the recorder 10 may be installed in the vicinity of the bed of the subject as a configuration that wirelessly transmits and receives the amplified signal with the amplifier 9 and records the bioelectric signal on the recording paper in real time. On the other hand, when the electrocardiogram measurement of a healthy person is performed by the bioelectric signal measuring device 7, the recorder 10 is electrically connected by the amplifier 9 and the conductive portion 11, and the bioelectric signal measurement data is stored in the memory. As a small-sized storage device, the subject carries the recorder 10 and continuously measures the electrocardiogram, and outputs the measurement data recorded in the memory when the subject returns home or visits the hospital. And it is sufficient.

  In the bioelectric signal measurement device of the present invention, the bioelectric signal measurement electrode is preferably used as a multipoint measurement electrode or a chest induction electrode. By using it as an electrode for multipoint measurement, bioelectric signals can be measured from many points on the body surface in the vicinity of the region to be measured, so that it can be measured more accurately than in the past. Further, when it is used as a chest lead electrode for the purpose of measuring an electrocardiogram signal, since the electrocardiogram signal can be measured from many body surfaces near the chest, the six chests generally used conventionally are used. Compared to the measurement using the electrode for measurement, more precise measurement can be performed. The chest induction electrode is disposed at a position covering the body surface near the region in front of the heart. For example, in the direction perpendicular to the body axis, the body surface near the left thoracic region is covered from the body surface near the subject's front sternum, and in the body axis direction, the body surface near the fourth rib is near the sixth rib (or seventh). It is arranged at a position covering the body surface near the rib, near the eighth rib, or near the lower edge of the rib.

Examples Examples of the bioelectric signal measurement electrode of the present invention will be described 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 Electrode for bioelectric signal measurement consisting of three concentric circles by using a stainless steel fiber (made by Nippon Seisen Co., Ltd., trade name: Naslon, twisted four stainless steel fibers with a diameter of 40 μm) (See FIG. 8). The produced bioelectric signal measurement electrode is composed of three concentric circle electrodes 2 as shown in FIG. 8, the outer circle having a diameter of 90 mm, the middle circle having a diameter of 60 mm, and the inner circle having a diameter of 30 mm. Thus, the width of each electrode 2 is 7 mm, and the distance between each electrode 2 is 2.3 mm. On the back surface of the woven fabric of the bioelectric signal measuring electrode, the stainless steel fibers were elongated from the woven ends of the electrodes 2, 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 bioelectric signal measurement electrode produced as described above was arranged so that the back surface of the electrode was 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: Waveron, electrical resistance: 1 × 10 ¹³ Ω / cm, official moisture content: 0.3%) 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 side made by using a twisted one and a stainless fiber with a diameter of 160μm (made by Nippon Seisen Co., Ltd., trade name: Naslon, a twist of four stainless fibers with a diameter of 40μm). A square electrode was used. FIG. 9 shows an electrocardiogram obtained by measuring the cardiac potential in a resting state using two of the three electrodes of the bioelectric signal measuring electrode and the reference ground electrode.

A Conductive region B Non-conductive region C Bioelectric signal measurement electrode 1 Fabric with multiple electrodes 2 Electrode 3 Conductive thread 4 Non-conductive thread 5 Conductive part 6 Insulator 7 Bioelectric signal measurement device 8 Clothes 9 Amplifier 10 Recorder 11 Conductive part

Claims (13)

Bioelectricity using a fabric with a multi-electrode comprising a plurality of electrodes composed of conductive regions by forming conductive regions and non-conductive regions by binding and weaving conductive yarns and non-conductive yarns a signal measuring electrodes,
An electrode for bioelectric signal measurement, characterized in that a non-conductive yarn is used for the warp, and a conductive yarn and a non-conductive yarn are used for the weft .   2. The bioelectric signal measuring electrode according to claim 1, wherein the conductive yarn is a stainless fiber, and the non-conductive yarn is a polyester yarn.   Bioelectricity using a fabric with a multi-electrode comprising a plurality of electrodes composed of conductive regions by forming conductive regions and non-conductive regions by binding and weaving conductive yarns and non-conductive yarns A signal measuring electrode,
  A bioelectric signal measuring electrode, wherein the conductive yarn is a stainless fiber and the non-conductive yarn is a polyester yarn.   4. The bioelectric signal measuring electrode according to claim 3, wherein the warp yarn and the weft yarn are weaved by using a non-conductive yarn for one of them and a conductive yarn for the other.   The bioelectric signal measurement electrode according to any one of claims 1 to 4, wherein the plurality of electrodes are spaced apart from each other and electrically insulated by a non-conductive region.   The bioelectric signal measuring electrode according to any one of claims 1 to 5, wherein a conductive portion formed by extending a conductive thread forming the electrode is formed from the electrode.   The bioelectric signal measurement electrode according to claim 6, wherein the conductive portion is covered with an insulator.   A bioelectric signal measurement device comprising the bioelectric signal measurement electrode according to claim 1. The bioelectric signal measurement electrode according to any one of claims 1 to 7,
An amplifier that amplifies the electrical signal detected by the biological signal measurement electrode and generates an amplified signal;
A bioelectric signal measurement device comprising: a recorder that records a bioelectric signal based on the amplified signal.   Furthermore, the electroconductive part which connects the said electrode for bioelectric signal measurement and an amplifier is provided, This electroconductive part is formed by extending | stretching the electroconductive thread | yarn which forms the said electrode for bioelectric signal measurement. The bioelectric signal measurement device according to 9.   The bioelectric signal measurement apparatus according to any one of claims 8 to 10, wherein the bioelectric signal is a myoelectric potential signal or a cardiac potential signal.   The bioelectric signal measurement device according to any one of claims 8 to 11, wherein the bioelectric signal measurement electrode is used as a multipoint measurement electrode.   The bioelectric signal measurement device according to any one of claims 8 to 11, wherein the bioelectric signal measurement electrode is used as a chest induction electrode.

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