Wearable band for measuring biological signals

Abstract

A wearable band for measuring biological signals according to an aspect of the present invention comprises: a plurality of biological electrodes; a measurement instrument connector to which a biological signal receiving device is connected; a first signal transmission unit that connects the plurality of biological electrodes and the measurement instrument connector; a chest support body having the plurality of biological electrodes, a non-stretchable part that supports the measurement instrument connector and the first signal transmission unit, and a stretchable part that is provided overlappingly to the non-stretchable part; and a pair of left and right stretchable strings connected to the left and right ends of the stretchable part and the non-stretchable part forming the chest support body. The pair of left and right stretchable strings each have a length adjustment mechanism and a connection mechanism, and fix the plurality of biological electrodes to a human body.

Description

Biosignal measurement harness

[0001] The present invention relates to a harness for measuring biological signals.

[0002] As the population ages in developed countries, deaths from cardiovascular disease are increasing worldwide. Routinely recording electrocardiograms over long periods of time and detecting abnormal arrhythmias early could provide opportunities for therapeutic intervention. Conventional 24-hour Holter electrocardiograms are unsuitable for daily use due to restrictions on bathing, short recording times, and low comfort. However, more comfortable wearable electrocardiograms have emerged in recent years, enabling long-term electrocardiogram recording. For example, patch-type electrocardiograms with adhesive bioelectrodes are known. Patent Document 1 and Non-Patent Document 1 are known as belt-type electrocardiograms that do not require an adhesive layer, respectively. Patent Document 2 is also known as an integrated belt-type electrocardiogram that measures electrocardiograms and respiratory rate. Also known are Patent Document 3, a wearable electrocardiograph for measuring multi-lead electrocardiograms that combines clothing with bioelectrodes having an adhesive layer, Patent Document 4, a pressure-wearable electrocardiograph equipped with bioelectrodes on a 2-way tricot fabric, Patent Document 5, a clothing for monitoring biosignals that has a ring-shaped torso, and implantable electrocardiographs that observe electrocardiograms on a yearly basis. Patent Document 6 is also known as a clothing for acquiring biosignals that uses localized elastic members to increase clothing pressure in order to improve adhesion between the living body and the electrodes.

[0003] Japanese Patent Publication No. 2008-520328 Japanese Patent Publication No. 2017-536896 Japanese Patent No. 7041986 Japanese Patent Application Laid-Open No. 2020-192391 International Publication No. 2021 / 177171 Japanese Patent Application Laid-Open No. 2022-150935

[0004] nuubo system Patient Instructions & Button Press Log, [Retrieved October 18, 2022], Internet <https: / / using.nuubo.com / wp-content / uploads / 2021 / 02 / 2406_IFU001_PATIENT-INSTRUCTIONS_EN_US_vC.pdf>

[0005] However, these wearable electrocardiographs pose several potential challenges. For example, potential challenges associated with wearing a patch-type electrocardiograph include the time required to position the bioelectrodes, sweating causing the adhesive layer to lose its grip and peel off, the need for a dressing to prevent peeling, skin irritation caused by the adhesive layer, discomfort caused by the weight of the electrocardiograph pulling the skin and adhesive layer, and epidermal damage and pain when removing the electrocardiograph. Potential challenges associated with wearing a belt-type electrocardiograph include discomfort caused by transverse pressure around the chest, and the increased body movement noise resulting from reduced pressure, which reduces the accuracy of the electrocardiogram. Potential challenges associated with wearing a shirt-type electrocardiograph include the time required to put on and take off the electrocardiograph, heat buildup due to the large fabric covering the body, and the need to prepare multiple sizes to fit the wearer's body type. Potential challenges associated with using an implantable electrocardiograph include the invasive nature of implantation and removal, the risk of surgical infection, and the generally high cost. In addition, in the case of a patch-type electrocardiograph or an implantable electrocardiograph, the number of leads used for electrocardiogram measurement is generally one.

[0006] The present invention has been made in view of these problems, and aims to provide a biosignal measurement harness that can be worn comfortably for long periods of time in daily life and that enables electrocardiogram measurement.

[0007] As a result of extensive research to solve the above problems and achieve the object, the present invention has been completed. That is, the present invention has any of the following configurations.

[0008] The biosignal measurement harness of the present invention is characterized in that it comprises: [1] a chest support having a plurality of bioelectrodes, a measuring instrument connector for connecting a biosignal receiving device, a first signal transmission unit for connecting the plurality of bioelectrodes and the measuring instrument connector, a non-stretchable unit for supporting the plurality of bioelectrodes, the measuring instrument connector, and the first signal transmission unit, and a stretchable unit superimposed on the non-stretchable unit; and a pair of left and right stretchable cords connected to the left and right ends of the non-stretchable unit and the stretchable unit that constitute the chest support, respectively, and the pair of left and right stretchable cords each having a length adjustment mechanism and a connecting mechanism for fixing the plurality of bioelectrodes to the human body.

[0009] Furthermore, the biosignal measurement harness of the present invention is characterized in that, in the invention described in [1] above, the pair of left and right elastic cords are a pair of left and right elastic waist cords, and when worn, the pair of left and right elastic waist cords pass over the sides of the body, cross or connect with each other in a sliding manner at the lower back, and then pass further over the sides of the body and connect in the front navel area or front lower abdominal area, thereby fixing the multiple bioelectrodes to the human chest.

[0010] Furthermore, the biosignal measurement harness of the present invention is [3] the invention described in [1] or [2] above, and is characterized in that it comprises a sternal manubrium support having one bioelectrode and a second signal transmission unit that connects the one bioelectrode to an electrode connector, an elastic conductive string that connects the chest support and the sternal manubrium support, and a pair of elastic shoulder straps, one end of which is connected to the sternal manubrium support and the other end of which is connected to the left and right ends of the elastic unit, respectively, wherein the elastic conductive string extends over the sternum to connect the first signal transmission unit and the second signal transmission unit, and the pair of elastic shoulder straps each have a length adjustment mechanism and a connecting mechanism, and when worn, they run from the sternal manubrium through the shoulders and down the sides of the body and connect to the left and right ends of the elastic unit, respectively, thereby fixing the one bioelectrode to the human sternal manubrium.

[0011] Furthermore, the biosignal measurement harness according to the present invention is [4] the invention described in [1] or [2] above, and is characterized in that it comprises a subclavian fossa support having one bioelectrode and a second signal transmission unit that connects the one bioelectrode to an electrode connector, an elastic conductive string that connects the chest support and the subclavian fossa support, and a pair of left and right elastic shoulder straps, one end of which is connected to the subclavian fossa support and the other end of which is connected to the left and right ends of the elastic part, respectively, wherein the elastic conductive string connects the first signal transmission unit and the second signal transmission unit, and the pair of left and right elastic shoulder straps each have a length adjustment mechanism and a connecting mechanism, and when worn, one of the shoulder straps passes from the shoulder on the subclavian fossa support side, passes over the side of the body, and connects to the end of the elastic part, and the other of the shoulder straps passes from the shoulder on the subclavian fossa support side, diagonally across the back, and connects to the other end of the elastic part, thereby fixing the one bioelectrode to the subclavian fossa.

[0012] The biosignal measurement harness according to the present invention comprises: [5] first, a lateral chest support having a plurality of bioelectrodes to be placed on the lateral chest, a measuring instrument connector for connecting a biosignal receiving device, a first signal transmission section connecting the plurality of bioelectrodes to the measuring instrument connector, a non-stretchable section for supporting the plurality of bioelectrodes, the measuring instrument connector, and the first signal transmission section, and a stretchable section provided overlaid on the non-stretchable section; second, a pair of left and right stretchable waist cords connected to left and right ends of the non-stretchable section and the stretchable section that constitute the lateral chest support, respectively; third, a subclavian fossa support having one bioelectrode and a second signal transmission section that connects the one bioelectrode to the electrode connector; fourth, a stretchable conductive cord connecting the lateral chest support and the subclavian fossa support; and fifth, one end of a wire connected to the subclavian fossa support and the other end of a wire and a pair of left and right elastic shoulder straps connected to the left and right ends of the elastic portion of the lateral chest support, respectively; sixth, the pair of left and right elastic waist straps each have a length adjustment mechanism and a connecting mechanism, and when worn, one passes along the side of the body, diagonally crosses the lower back, and further passes along the side of the body, extending to the navel or lower abdomen on the front, and the other extends from the back, along the side of the body, and to the navel or lower abdomen on the front, and then connected, thereby fixing the multiple bioelectrodes to the chest of the human body; seventh, the pair of left and right elastic shoulder straps each have a length adjustment mechanism and a connecting mechanism, and when worn, one passes along the shoulder of the infraclavicular fossa, crosses the front, passes along the side of the body, and connects to an end of the elastic portion, and the other passes along the shoulder of the infraclavicular fossa, diagonally crosses the back, and connects to the other end of the elastic portion, thereby fixing one bioelectrode to the infraclavicular fossa.

[0013] Furthermore, the biosignal measurement harness according to the present invention is [6] the invention described in [3] or [4] above, characterized in that the chest support covers the upper part of the human chest, or covers the upper part of the human chest in combination with a detachable chest covering.

[0014] Furthermore, the biosignal measurement harness of the present invention is characterized in that, in the invention described in any one of [1] to [4] above, the coverage area is 30% or less of the front of the wearer's trunk and 20% or less of the back of the wearer's trunk.

[0015] Furthermore, the biosignal measurement harness of the present invention is characterized in that, in the invention described in any one of [1] to [7] above, at least one of the bioelectrodes has a buffer layer on the back surface thereof, in which buffer materials with different compressive stresses are laminated.

[0016] Furthermore, the biosignal measurement harness of the present invention is characterized in that, in the invention described in [8] above, the compressive stress of the buffer material constituting the buffer layer on the bioelectrode side is smaller than the compressive stress on the side opposite to the bioelectrode side.

[0017] Furthermore, the biosignal measurement harness of the present invention is

[10] an invention described in any one of [1] to [4] and [6] to [9] above, characterized in that the arrangement of the bioelectrodes follows any one of (a) CC5 lead, (b) CM5 lead, (c) NASA lead, (d) CC5 lead and CM5 lead, (e) CC5 lead and NASA lead, (f) CM5 lead and NASA lead, (g) CC5 lead, CM5 lead and NASA lead, and (h) EASI lead.

[0018] Furthermore, the biosignal measurement harness of the present invention is characterized in that, in the invention described in any one of [1] to

[10] above, a converter is used to connect at least one or more of the biosignal receiving devices.

[0019] The harness for measuring biological signals of the present invention allows a plurality of biological electrodes supported by the chest support body to come into contact with the skin of the human chest.

[0020] FIG. 1A is a front view of an example of a configuration of a biosignal measurement wearing belt according to a first embodiment of the present invention. FIG. 1B is a rear view of an example of a configuration of a biosignal measurement wearing belt according to the first embodiment of the present invention. FIG. 1C is a side view of an example of a configuration of a biosignal measurement wearing belt according to the first embodiment of the present invention. FIG. 2A is a front view of an example of a configuration of a biosignal measurement wearing belt according to a second embodiment of the present invention. FIG. 2B is a rear view of an example of a configuration of a biosignal measurement wearing belt according to the second embodiment of the present invention. FIG. 2C is a side view of an example of a configuration of a biosignal measurement wearing belt according to the second embodiment of the present invention. FIG. 3A is a front view of an example of a configuration of each part of a raw signal measurement wearing belt according to the second embodiment of the present invention. FIG. 3B is a rear view of an example of a configuration of each part of a raw signal measurement wearing belt according to the second embodiment of the present invention. FIG. 3C is a top view of an example of a configuration of each part of a raw signal measurement wearing belt according to the second embodiment of the present invention. FIG. 4A is a view from the front of a biosignal measurement harness according to a first modification of the second embodiment of the present invention. FIG. 4B is a view from the back of a biosignal measurement harness according to the first modification of the second embodiment of the present invention. FIG. 5A is a view from the front of a biosignal measurement harness according to a second modification of the second embodiment of the present invention. FIG. 5B is a view from the back of a biosignal measurement harness according to a second modification of the second embodiment of the present invention. FIG. 6A is a view from the front of an example of a configuration of an epigastric buffer layer according to the second embodiment of the present invention. FIG. 6B is a view from the back of an example of a configuration of an epigastric buffer layer according to the second embodiment of the present invention. FIG. 6C is a side view of an example of a configuration of an epigastric buffer layer according to the second embodiment of the present invention. FIG. 6D is a side view of a modification of the example of the epigastric buffer layer according to the second embodiment of the present invention when worn. FIG. 7 is a view from the front of an example of a configuration of a first signal transmission unit according to the second embodiment of the present invention. FIG. 8A is a view from the front of a manubrium support according to a third modification of the second embodiment of the present invention. Figure 8B is a rear view of the sternal manubrium support according to Modification 3 of Embodiment 2 of the present invention. Figure 8C is a side view of the sternal manubrium support according to Modification 3 of Embodiment 2 of the present invention. Figure 9A is a front view of an example configuration of the sternal manubrium support according to Embodiment 2 of the present invention. Figure 9B is a side view of an example configuration of the sternal manubrium support according to Embodiment 2 of the present invention.FIG. 9C is a rear view of an example configuration of a sternal manubrium support according to the second embodiment of the present invention. FIG. 9D is a side view of a modified example of a configuration of a sternal manubrium cushioning layer according to the second embodiment of the present invention when worn. FIG. 10A is a diagram showing an example configuration of a second signal transmission unit according to the second embodiment of the present invention. FIG. 10B is a diagram showing an example configuration of a second signal transmission unit and an epigastric cushioning layer according to the second embodiment of the present invention. FIG. 11A is a perspective view of an example configuration of a converter connecting two electrocardiographs. FIG. 11B is an exploded view showing an example configuration of a converter connecting two electrocardiographs in an exploded state. FIG. 12A is a front view of an example wearing example of a biosignal measurement harness according to the third embodiment of the present invention. FIG. 12B is a rear view of an example wearing example of a biosignal measurement harness according to the third embodiment of the present invention. FIG. 12C is a right side view of an example wearing example of a biosignal measurement harness according to the third embodiment of the present invention. FIG. 12D is a left side view of an example wearing example of a biosignal measurement harness according to the third embodiment of the present invention. FIG. 13A is a front view of a wearing example of the biosignal measurement harness according to embodiment 4 of the present invention. FIG. 13B is a back view of a wearing example of the biosignal measurement harness according to embodiment 4 of the present invention. FIG. 13C is a right side view of a wearing example of the biosignal measurement harness according to embodiment 4 of the present invention. FIG. 13D is a left side view of a wearing example of the biosignal measurement harness according to embodiment 4 of the present invention. FIG. 14A is an oblique view of a configuration example of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 14B is an enlarged view of a connecting portion of the sternal manubrium support of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 14C is an enlarged view of a connecting portion of the stretchable portion of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 15 is a front view of a configuration example of a chest cover of the biosignal measurement harness according to embodiment 6 of the present invention. FIG. 16A is a front view of the biosignal monitoring wear of Comparative Example 1. Fig. 16B is a side view of the biosignal monitoring wear shown in Fig. 16A. Fig. 16C is a back view of the biosignal monitoring wear shown in Fig. 16A. Fig. 17 is a 30-minute electrocardiogram (CC5 lead) taken while wearing the biosignal measurement harness of Example 1 (while sleeping).18 is a diagram showing the relationship between the sum of the chest and waist circumferences of a wearer of the biosignal measurement harness of Example 2 and the length of the elastic waist cord before wearing. FIG. 19 is a diagram showing the relationship between the shoulder circumference of a wearer of the biosignal measurement harness of Example 2 and the length of the elastic shoulder straps before wearing. FIG. 20A is a diagram showing contact pressure (air pack type) measured at positions where five bioelectrodes in the biosignal measurement harness of Example 2 contact the wearer's skin when wearing the biosignal measurement harness of Example 2 or the biosignal monitoring wear of Comparative Example 1. FIG. 20B is a diagram showing the time change of a 5-second electrocardiogram (from top to bottom: CC5 lead, CM5 lead, and NASA lead) and three-axis acceleration (solid line X: up-down direction, dashed line Y: left-right direction, dashed line Z: front-back direction) when wearing the biosignal measurement harness of Example 2 (standing at rest and walking). 21A is a diagram showing a 20-second electrocardiogram (from top to bottom, CC5 lead, CM5 lead, and NASA lead) and time-dependent changes in triaxial acceleration (solid line X is the up-down direction, dashed line Y is the left-right direction, and dashed line Z is the front-to-back direction) when wearing the biosignal measurement harness of Example 2 (at rest). FIG. 21B is a diagram showing a 20-second electrocardiogram (from top to bottom, CC5 lead, CM5 lead, and NASA lead) and time-dependent changes in triaxial acceleration (solid line X is the up-down direction, dashed line Y is the left-right direction, and dashed line Z is the front-to-back direction) when wearing the biosignal measurement harness of Example 2 (while running on flat ground). FIG. 21C is a diagram showing a 3-minute electrocardiogram (from top to bottom, CC5 lead, CM5 lead, and NASA lead) and time-dependent changes in triaxial acceleration (solid line X is the up-down direction, dashed line Y is the left-to-right direction, and dashed line Z is the front-to-back direction) when wearing the biosignal measurement harness of Example 2 (while performing radio calisthenics No. 1). Fig. 21D is a diagram showing the electrocardiogram acquisition rate (leads AS, ES, and IS), hourly average values ​​of the activity score acc, and the number of steps per hour for seven non-consecutive days in period 1 when the biosignal measurement harness of Example 2 is worn (during daily life). Fig. 21E is a diagram showing the electrocardiogram acquisition rate (leads AS, ES, and IS), hourly average values ​​of the activity score acc, and the number of steps per hour for seven consecutive days in period 2 when the biosignal measurement harness of Example 2 is worn (during daily life). Fig. 22 is a diagram showing the dressing time and undressing time for Example 2 or Comparative Example 1. Fig. 23 is a diagram showing the relationship between the elongation rate and elongation load of the elastic waist strap, elastic shoulder straps, and elastic conductive straps of Example 4.Figure 24 shows contact pressure (air pack type) measured at the positions where the five bioelectrodes of the biosignal measurement harness of Example 4 contact the wearer's skin when the biosignal measurement harness of Example 4 is worn. Figure 25 shows a surface temperature distribution image captured with a thermographic camera when the biosignal measurement harness of Example 4 is worn. Figure 26A shows the relationship between the compressibility and compressive stress of the epigastric buffer layer in each of Examples 6-1 and 2, and the relationship between the compressibility and compressive stress of the manubrium buffer layer in each of Examples 6-2 to 6-7 and Example 2. Figure 26B shows the structure of the epigastric buffer layer in each of Examples 6-1 and 2, and the structure of the manubrium buffer layer in each of Examples 6-2 to 6-7 and Example 2. FIG. 27 shows a 5-second electrocardiogram and time-dependent changes in three-axis acceleration (solid line X indicates the up-down direction, dashed line Y indicates the left-right direction, and dashed line Z indicates the front-back direction) when the biosignal measurement harness of Example 7 or Example 8 is worn (while standing at rest and while walking).

[0021] Preferred embodiments of the biosignal measurement harness according to the present invention will be described in detail below with reference to the drawings. Note that the present invention is not limited to the following embodiments. It should be noted that the drawings are schematic, and the dimensional relationships and ratios of each element may differ from those in reality. The drawings may also include parts with different dimensional relationships and ratios. In addition, the same components are designated by the same reference numerals in each drawing. The term "wearer" refers to a person who wears the biosignal measurement harness according to an embodiment of the present invention.

[0022] In the present invention, unless otherwise specified, "rear surface" refers to the surface facing the wearer's skin (skin, living body) (the surface facing the skin). Furthermore, unless otherwise specified, "front surface" refers to the surface opposite to the "rear surface". The definitions of "rear surface" and "front surface" above also apply to each part of the biosignal measurement harness. "Lead" refers to the direction in which the electrical flow of the heart is observed in electrocardiogram recording.

[0023] (Embodiment 1) FIG. 1A is a front view of an example of a configuration of a raw signal measurement harness according to embodiment 1 of the present invention. FIG. 1B is a rear view of an example of a configuration of a raw signal measurement harness according to embodiment 1 of the present invention. FIG. 1C is a side view of an example of a configuration of a raw signal measurement harness according to embodiment 1 of the present invention. As shown in FIGS. 1A to 1C, a biological signal measurement harness 100 according to embodiment 1 is composed of a chest support 2 and a pair of left and right elastic waist cords 4. The chest support 2 supports bioelectrodes (not shown) that are to be brought into contact with the wearer's skin. The chest support 2 of embodiment 1 also comprises a non-stretchable section (not shown) that includes the bioelectrodes (e.g., multiple bioelectrodes) and a first signal transmission section 24 that connects the bioelectrodes to a measurement instrument connector 51, and an elastic section 23 that is provided over the non-stretchable section. A biological signal receiving device (not shown) is connected to this measurement instrument connector 51. The first signal transmission unit 24 is composed of conductive fiber 8 and seam tape 10. The elastic waist cord 4 is an example of a pair of elastic cords connected to the left and right ends of the non-elastic portion and the elastic portion 23 constituting the chest support 2. In this embodiment, it is preferable that one end of the elastic waist cord 4 is connected to the non-elastic portion and its middle is connected to the left and right ends of the elastic portion 23. It is also preferable that the elastic waist cord 4 is connected to the surface of the elastic portion 23. When worn, the elastic portion 23 stretches together with the elastic waist cord 4. The bioelectrodes are preferably connected to the conductive fiber 8 by electrode connectors 52. In the biosignal measurement harness 100, the chest support 2 supports three bioelectrodes, four measurement instrument connectors 51, and three electrode connectors 52. However, the number and arrangement of these connectors are not limited to this and can be arbitrarily combined depending on the purpose of biosignal measurement and the type and number of biosignal receiving devices.

[0024] The biosignal measurement harness 100 allows the pair of elastic waist cords 4 to be wound spirally around the wearer's torso while being stretched, thereby bringing the bioelectrodes (not shown) of the chest support 2 into contact with the skin. Specifically, the elastic waist cords 4, which are connected to the left and right ends of the non-elastic and elastic portions 23 constituting the chest support 2, pass along the sides of the body, cross or connect in a sliding manner at the lower back, and then pass along the sides and connect in the front umbilical or lower abdominal area, thereby securing the chest support 2 supporting multiple bioelectrodes to the human chest. The connection method is not particularly limited, and the pair of elastic waist cords 4 may be connected crosswise or non-crosswise using hooks such as ring hooks or eight-ring hooks. Furthermore, in the case of the biosignal measurement harness 100, the pair of elastic waist cords 4 spirally wrap around the torso approximately 1.5 times, whereas in the case of a belt-type electrocardiograph, the belt wraps horizontally around the chest approximately 0.5 times. If the elastic waist cord 4 and the belt are made of the same material and have the same elongation rate, an elastic waist cord 4 that spirals around the torso 1.5 times will experience a smaller change in elongation stress with increasing chest circumference due to inhalation than a belt that horizontally wraps around the chest 0.5 times, thereby reducing the sense of pressure on the chest. This configuration allows the biosignal measurement harness 100 to avoid chest compression compared to belt-type electrocardiographs and minimizes changes in pressure with changes in the wearer's chest circumference. Furthermore, when worn, the elongation stress of the pair of elastic waist cords 4 is transmitted to the non-elastic portions of the chest support 2. The vectors of these elongation stresses change along the curved surface around the wearer's chest, generating a force that presses the chest support 2, including the non-elastic portions, against the wearer's skin. This allows bioelectrodes (not shown) to contact the skin without using an adhesive layer, reducing discomfort associated with wearing the harness compared to conventional Holter electrocardiographs and patch-type electrocardiographs. Furthermore, the elastic waist cords 4 can each have a length adjustment mechanism and a connecting mechanism. For example, as shown in Figure 1A, if a pair of elastic waist cords 4 are provided with front hooks 43 and eight-hook claws 44, the biosignal measurement harness 100 can be made one size fits all, allowing it to be adapted to wearers with various body types with different torso and chest circumferences. Furthermore, if the length of the elastic waist cords 4 is insufficient for the wearer's body type, the length can be extended by connecting independent elastic members.

[0025] (Embodiment 2) Fig. 2A is a front view of an example of the configuration of a harness for measuring raw signals according to embodiment 2 of the present invention. Fig. 2B is a rear view of an example of the configuration of a harness for measuring raw signals according to embodiment 2 of the present invention. Fig. 2C is a side view of an example of the configuration of a harness for measuring raw signals according to embodiment 2 of the present invention. As shown in Figs. 2A to 2C, the harness for measuring biological signals 101 according to embodiment 2 is composed of a chest support member 2A, a sternal manubrium support member 3, a pair of elastic waist straps 4, a pair of elastic shoulder straps 5, and an elastic conductive strap 6. The chest support member 2A and the sternal manubrium support member 3 serve to support a biological electrode 7.

[0026] FIG. 3A is a front view of an example of the configuration of each part of the raw signal measurement harness according to embodiment 2 of the present invention. FIG. 3B is a back view of an example of the configuration of each part of the raw signal measurement harness according to embodiment 2 of the present invention. FIG. 3C is a top view of an example of the configuration of each part of the raw signal measurement harness according to embodiment 2 of the present invention. As shown in FIG. 3B , in the biosignal measurement harness 101 according to embodiment 2, the chest support member 2A can support multiple bioelectrodes 7 (e.g., four bioelectrodes 7a, 7b, 7c, and 7d) in contact with the human chest. The sternal manubrium support member 3 can support one bioelectrode 7 (e.g., bioelectrode 7e) in contact with the human manubrium. In FIG. 3A , the chest support member 2A is composed of a first signal transmission unit 24A that connects the multiple bioelectrodes 7 to the measurement instrument connector 51, a non-stretchable unit 25, and a stretchable unit 23A. A biosignal receiving device (not shown) is connected to the measuring instrument connector 51. The chest support 2A and the sternal manubrium support 3 are connected by the elastic conductive strings 6 and a conductive connector (not shown). The sternal manubrium support 3 may be provided with a conductive connector 53 (see FIG. 9A ) to which the elastic conductive strings 6 are connected, and a second signal transmission unit 34 (see FIG. 10A ) to which the electrode connector 52 and the conductive connector 53 are connected. In the second embodiment of the present invention, the chest support 2A supports four bioelectrodes 7a, 7b, 7c, and 7d, five measuring instrument connectors 51, and four electrode connectors 52. However, the number and arrangement of these components are not limited to this and can be arbitrarily combined depending on the purpose of biosignal measurement and the type and number of biosignal receiving devices.

[0027] The biosignal measurement harness 101 allows multiple bioelectrodes 7 (e.g., four bioelectrodes 7a, 7b, 7c, and 7d) supported by the chest support 2A and one bioelectrode 7e supported by the sternal manubrium support 3 to contact the wearer's skin. In addition to the components of the first embodiment, the second embodiment also includes a sternal manubrium support 3, an elastic conductive cord 6, and a pair of elastic shoulder straps 5. The pair of elastic shoulder straps 5 are connected to the left and right ends of the non-elastic portion 25 and the elastic portion 23A of the chest support 2A, respectively. Preferably, the pair of elastic shoulder straps 5 start from the wearer's manubrium, pass through the clavicles and scapulae, and pass along the sides of the body, and connect to the ends of the elastic portion 23A. Furthermore, the elastic conductive cord 6 extends over the sternum and connects the first signal transmission unit 24A of the chest support 2A to the second signal transmission unit 34 (see FIG. 10A ) of the sternal manubrium support 3. When worn, the non-stretchable portion 25 of the chest support 2A is subjected to tensile stresses from the pair of elastic waist straps 4, the pair of elastic shoulder straps 5, and the elastic conductive cord 6. The vectors of these tensile stresses change along the curved surface around the wearer's chest, generating a force that presses the chest support 2A, including the non-stretchable portion 25, against the wearer's skin. Similarly, the sternal manubrium support 3 is subjected to tensile stresses from the pair of elastic shoulder straps 5 and the elastic conductive cord 6. The vectors of these tensile stresses change along the curved surface around the wearer's chest, generating a force that presses the sternal manubrium support 3 against the wearer's skin. Therefore, the chest support 2A and the sternal manubrium support 3 can each bring the four bioelectrodes 7a, 7b, 7c, and 7d and one bioelectrode 7e into contact with the wearer's skin.

[0028] When the wearer wears the biosignal measurement harness 101, the bioelectrode 7e supported by the sternal manubrium support 3 can be positioned in the area surrounded by the upper, lower, left, and right ends of the sternal manubrium, and the four bioelectrodes 7a, 7b, 7c, and 7d supported by the chest support 2A can be positioned in the area surrounded by the upper end of the fourth rib, the lower end of the seventh rib, and the left and right posterior axillary lines. The elastic conductive cord 6 extends over the sternum, the pair of elastic shoulder straps 5 pass over the left and right clavicles and scapulae, respectively, and the pair of elastic waist straps 4 pass over the left and right sides of the body, cross or connect with each other in a sliding manner at the lower back, and then pass over the sides of the body and connect at the navel or lower abdominal area on the front. In one example of how to wear the biosignal measurement harness 101, the wearer's shoulder length (the length of line A-A' in FIG. 2C), chest length (the circumference at position B in FIG. 2C), and waist length (the circumference at position C in FIG. 2C) are first measured. Next, the length of the elastic waist straps 4 is adjusted to fit the wearer's body shape, and the length of the elastic shoulder straps 5 is adjusted to fit the wearer's body shape, as shown in FIG. 18. Then, after placing the pair of elastic shoulder straps 5 on each shoulder, the left and right hands grasp the connection between the elastic portions 23A on the left and right sides of the chest support 2A and the elastic waist straps 4, respectively, and stretch the chest support 2A horizontally while placing it against the human chest, bringing the bioelectrodes into contact with the skin. Next, the grasping hands are slid toward the ends of the elastic waist straps 4, drawing the elastic waist straps 4 to the lower back, so that they cross each other in a sliding manner. The handle of the elastic waist cord 4 is then replaced, and the ends of the elastic waist cord 4 are again pulled out to the front of the body and connected in the front navel or front lower abdominal area to put on the biosignal measurement harness 101. At this time, the wearer's arms move downwards from shoulder height, making it easier to put on than a wearable electrocardiograph, in which the arms are raised above the shoulders and the device is put on over the head. Furthermore, the biosignal measurement harness 101 can be easily taken off by simply removing both arms from the elastic shoulder straps 5 after releasing the connection between the ends of the elastic waist cord 4. In this way, the biosignal measurement harness 101 has the advantage that it can be put on and taken off in a short time.

[0029] Not only the biosignal measurement harness 100 shown in FIGS. 1A to 1C , but also the biosignal measurement harness 101 shown in FIGS. 2A to 2C have a small skin area that is less likely to trap heat. In the case of the biosignal measurement harness 101, the area covering the front of the wearer's trunk is preferably 30% or less of the area of ​​the front of the wearer's trunk, and the area covering the back of the wearer's trunk is preferably 20% or less of the area of ​​the back of the wearer's trunk. Here, the trunk refers to the torso excluding the neck, arms, and legs. The area covering the front or back of the trunk refers to the area occupied by the front or back of the biosignal measurement harness 101 worn on the torso relative to the front or back of the torso's trunk. The area ratio can be calculated by printing photographs of the torso and the front and back of the biosignal measurement harness 101 worn on the torso on cardboard, cutting out the corresponding portions, and calculating the weight ratio of the front and back of the cardboard.

[0030] The appearance of the biosignal measurement harness 101 and its combination with clothing will now be described. When worn, the sternal manubrium support 3 can be hidden with a crew neck short-sleeved shirt, and it can be worn with everyday clothing such as a dress shirt, blouse, or sweater. Furthermore, when the wearer wears a brassiere, the order in which the biosignal measurement harness 101 and the brassiere are worn can be changed based on the height of the brassiere cup base. That is, if the brassiere cup base is high, it is preferable to wear the biosignal measurement harness 101 under the brassiere (underside) and place the bioelectrodes 7 in contact with the skin. On the other hand, if the brassiere cup base is low, the biosignal measurement harness 101 may be worn over the brassiere (front) so that the upper end of the chest support 2A partially overlaps the bra, and the bioelectrodes 7 may be in contact with the skin. Alternatively, the biosignal measurement harness 101 may be worn using a foldable, flat transducer (not shown) that electrically connects the measurement instrument connector 51 of the biosignal measurement harness 101 to a biosignal receiving device (not shown). In this case, the bottom edge of the brassiere cup base and the fold (the boundary when folded) of the transducer are close to each other, and the side of the transducer that connects to the measuring instrument connector 51 can be placed under (on the back side of) the brassiere cup base, while the side that connects to the biosignal receiving device can be placed on (on the front side of) the brassiere cup base. The ends of the transducer on the opposite side of the fold can also be connected with a clip, hook-and-loop fastener, hook-and-loop fastener, snap button, string, or the like. Using such a transducer allows the biosignal measurement harness 101 to be attached under (on the back side of) the brassiere, regardless of the height of the cup base, even when the brassiere is being worn, thereby increasing convenience. Furthermore, the path of the elastic shoulder straps 5 is characterized by being different from the path of the bra's shoulder straps, as shown in FIG. 2B .

[0031] The biosignal measurement harness 101 has length adjustment mechanisms on the elastic shoulder straps 5 and elastic waist straps 4. Therefore, the wearer can adjust the pressure by inserting their hands through the collar or hem of their everyday clothing to change the length of the elastic shoulder straps 5 and elastic waist straps 4. This allows the wearer to adjust the pressure to suit daily changes in body shape. For example, if the waist circumference temporarily increases after eating or drinking, the elastic waist strap 4 can be lengthened to reduce the pressure on the chest. Furthermore, if the wearer becomes sensitive to pressure due to changes in physical condition or mental state, the elastic waist straps 4 and elastic shoulder straps 5 can be lengthened to reduce the pressure on the manubrium and chest. On the other hand, during physical activity, the contact between the bioelectrodes 7 and the skin is likely to become unstable, so the elastic waist straps 4 and elastic shoulder straps 5 can be shortened to increase the pressure.

[0032] As shown in FIG. 3A , the chest support 2A preferably comprises an elastic section 23A, a first signal transmission section 24A, and a non-elastic section 25. The first signal transmission section 24A is preferably sandwiched between the front surface of the elastic section 23A and the rear surface of the non-elastic section 25. The left and right elastic shoulder straps 5 are preferably connected to the left and right ends of the elastic section 23A, respectively, and the left and right elastic waist straps 4 are preferably connected to the left and right ends of the elastic section 23A and the non-elastic section 25, respectively. The elastic conductive cord 6 is preferably connected to the upper center of the non-elastic section 25. The chest support 2A has a measuring instrument connector 51, which can be connected to a biosignal receiving device (not shown) to receive or record biosignals. Furthermore, a buffer layer is preferably provided on the rear surface of the bioelectrode 7 of the chest support 2A. In particular, an epigastric buffer layer 21 is preferably provided on the rear surface of the bioelectrode 7c. As shown in FIG. 3C, it is also preferable to have an epigastric pocket 22 between the stretchable portion 23A and the non-stretchable portion 25, which accommodates the epigastric cushioning layer 21.

[0033] Fig. 4A is a front view of a biosignal measurement harness according to a first variation of the second embodiment of the present invention. Fig. 4B is a back view of the biosignal measurement harness according to the first variation of the second embodiment of the present invention. As shown in Figs. 4A and 4B, the biosignal measurement harness 102 differs from the biosignal measurement harness 101 in that the elastic waist cord connection mechanism includes a hook-and-loop fastener 48A at the end of the elastic waist cord 4R and multiple hook-and-loop fastener loops 48B arranged at equal intervals from the end of the elastic waist cord 4L. Therefore, the compression can be adjusted by changing the position of the hook-and-loop loops 48B that secure the hook-and-loop fastener 48A to change the elongation rate.

[0034] Fig. 5A is a front view of the biosignal measurement harness according to Variation 2 of Embodiment 2 of the present invention. Fig. 5B is a back view of the biosignal measurement harness according to Variation 2 of Embodiment 2 of the present invention. As shown in Figs. 5A and 5B , the biosignal measurement harness 103 differs from the biosignal measurement harness 101 in the arrangement of the multiple bioelectrodes 7 (e.g., four bioelectrodes 7a, 7b, 7c, and 7d) on the chest support 2B. The biosignal measurement harness 103 also has a first signal transmission unit 24B that can directly connect two biosignal receiving devices (not shown) to the chest support 2B.

[0035] Fig. 6A is a front view of an example of an epigastric cushioning layer according to embodiment 2 of the present invention, in an example where a cushioning layer is provided, which is a preferred aspect of the present invention. Fig. 6B is a back view of an example of an epigastric cushioning layer according to embodiment 2 of the present invention. Fig. 6C is a side view of an example of an epigastric cushioning layer according to embodiment 2 of the present invention. Fig. 6D is a side view of a modified example of the epigastric cushioning layer according to embodiment 2 of the present invention when worn. As shown in Fig. 6D, the epigastric pocket 22 is formed by an elastic portion 23A and a non-elastic portion 25. Furthermore, as shown in Fig. 6C, the epigastric cushioning layer 21 preferably has a stacked cushioning material structure, i.e., a stacked structure of a first epigastric cushioning layer 211 and a second epigastric cushioning layer 212. As shown in FIG. 6A , the second-layer epigastric cushioning material 212 is provided with mechanical fastener hooks 213, which can be fastened to mechanical fastener loops 214 (see FIG. 3C ) inside the epigastric pocket 22. The purposes of providing the epigastric cushioning layer 21 are as follows: First, the epigastric cushioning layer 21 fills the gap between the skin and the chest support 2A, thereby promoting contact of the epigastric bioelectrode 7 (e.g., 7c) with the skin. Second, the epigastric cushioning layer 21 transmits the force pressing the chest support 2A against the living body to the epigastric bioelectrode 7 (e.g., 7c). Furthermore, the epigastric cushioning layer 21 deforms in accordance with changes in the shape of the epigastric region due to muscle and diaphragm movements associated with walking, running, and breathing, promoting contact of the bioelectrode 7 (e.g., 7c) with the skin. For example, the epigastric cushioning layer 21 may deform as shown in FIG. 6D when worn. The epigastric buffer layer 21 absorbs vibrations transmitted to the epigastric region during walking and running, and assists the contact of the bioelectrode 7 (e.g., bioelectrode 7c, etc.) with the skin. In addition, increasing the thickness of the epigastric buffer layer 21 can increase the contact pressure of the epigastric bioelectrode 7 (e.g., bioelectrode 7c, etc.) with the skin. The contact pressure of the epigastric bioelectrode 7 (e.g., bioelectrode 7c, etc.) with the skin can also be increased by increasing the compressive stress of the buffer material. However, excessively increasing the contact pressure can cause discomfort to the wearer, so an appropriate load must be set. Furthermore, stacking buffer materials has the following advantages.That is, as shown in Figures 26A and 26B, compared to a single cushioning material (Example 6-1), the laminated cushioning material (Example 2) generates a wider range of compressive stress when the compression ratio is changed. Therefore, even when the pressure applied to the epigastrium changes during wear, it can respond better than a single cushioning material. Furthermore, according to the compressive stress measurements of the cushioning material or buffer layer described below, the epigastrium buffer layer 21 of Example 2 generates a compressive stress of 100 g to 500 g at a compression ratio of 5% to 30% and a compressive stress of 400 g to 1400 g at a compression ratio of 30% to 50%. For example, when the diameter of the epigastrium buffer layer 21 is 4.5 cm, the compressive stress is 6.3 g / cm at a compression ratio of 5% to 30%. ２ 31g / cm or more ２ The following loads are applied: 25 g / cm when the compression rate is 30% or more and 50% or less. ２ 88g / cm or more ２ This corresponds to the following load:

[0036] For a more comfortable fit, the characteristics of the epigastric buffer layer 21 are preferably a compressibility of 5% to 50% and a compressive stress of 25 g to 2000 g, more preferably a compressive stress of 50 g to 1500 g, and even more preferably a compressive stress of 100 g to 1000 g. Furthermore, if the wearer's epigastric region is recessed, it is preferable to use the epigastric buffer layer 21. However, if the epigastric region is not recessed due to fat or the like, it is not necessary to use the epigastric buffer layer 21 to increase contact pressure, and the epigastric buffer layer 21 can be worn without being fixed to the biosignal measurement harness. In other words, it is preferable that the epigastric buffer layer 21 be detachable.

[0037] FIG. 7 is a front view of an example configuration of the first signal transmission unit according to the second embodiment of the present invention. As shown in FIG. 7 , the first signal transmission unit 24A is composed of conductive fibers 8 and a seam tape 10. Bioelectrodes (not shown) supported by the chest support 2A are connected to the conductive fibers 8 via electrode connectors 52a, 52b, 52c, and 52d. Bioelectrodes (not shown) supported by the manubrium support 3 are connected to the conductive fibers 8 via an electrode connector 52e. A biosignal receiving device (not shown) is connected to the conductive fibers 8 via a measuring instrument connector 51. The first signal transmission unit 24A serves to connect the bioelectrodes (not shown), the elastic conductive string 6, the measuring instrument connector 51, and the electrode connectors 52a, 52b, 52c, and 52e. The seam tape 10 serves as an insulator to prevent unintended electrical connection between the conductive fibers 8. The electrode connector 52c is connected to the bioelectrode 7c from inside the epigastric pocket 22 by folding back at the line segment E-E' (see FIG. 3C ). At this time, the core wire of the electric wire 61 of the stretchable conductive cord 6 can be connected directly to the measurement instrument connector 51 or indirectly via the conductive fiber 8 or a conductor. In FIG. 7 , the stretchable conductive cord 6 is fixed to the first signal transmission unit 24A including the conductive fiber 8. However, the stretchable conductive cord 6 may be detachably fixed to the first signal transmission unit 24A including the conductive fiber 8 using, for example, a conductive snap button. The shape of the first signal transmission unit 24A shown in FIG. 7 is merely an example and can be freely changed to match the shape of the biosignal measurement harness.

[0038] Figure 8A is a front view of the sternal manubrium support according to Modification 3 of Embodiment 2 of the present invention. Figure 8B is a back view of the sternal manubrium support according to Modification 3 of Embodiment 2 of the present invention. Figure 8C is a side view of the sternal manubrium support according to Modification 3 of Embodiment 2 of the present invention. As shown in Figures 8A to 8C, the sternal manubrium support 3A has a conductive connector 53 located at its center, and is connected to the elastic conductive string 6 on the front side and the bioelectrode 7 on the back side. The sternal manubrium support 3A also has a sternal manubrium connecting loop 32 for connecting the elastic shoulder strap 5.

[0039] Considering the influence of body movement on biosignal measurement, the muscles and skin around the manubrium tend to move in conjunction with arm and neck movements, causing body movement noise in electrocardiograms. For example, when a wearer extends their arm forward, the muscles and clavicle move forward, and when the wearer tilts their head up, down, left, or right, the skin around the manubrium moves in conjunction with neck movement. Such movements disrupt contact between the manubrium bioelectrode 7e and the skin, resulting in body movement noise being mixed into electrocardiograms in CM5 and NASA leads, which use the manubrium bioelectrode 7e as the negative electrode for bipolar leads. Therefore, in the present invention, when body movement is involved, it is preferable to use a manubrium support with a buffer layer instead of variant 3 of embodiment 2. For example, variant 3 of embodiment 2 uses two manubrium support members 33A and a buffer material F. ６ A sternal manubrium support 3A can be used, which sandwiches a sternal manubrium cushioning layer (material: ethylene vinyl acetate copolymer foam, thickness 4 mm). Furthermore, a sternal manubrium support 3 with a cushioning layer can be used, which is combined with a sternal manubrium cushioning layer 31 (see Figure 9B), which will be described later. This further improves the contact between the bioelectrode 7e on the sternal manubrium and the skin, reducing body movement noise in electrocardiograms.

[0040] Figure 9A is a front view of an example of a configuration of a sternal manubrium support according to a preferred embodiment of the present invention. Figure 9B is a side view of an example of a configuration of a sternal manubrium support according to the second embodiment of the present invention. Figure 9C is a rear view of an example of a configuration of a sternal manubrium support and a sternal manubrium cushioning layer according to the second embodiment of the present invention. Figure 9D is a side view of a modified example of a configuration of a sternal manubrium cushioning layer according to the second embodiment of the present invention when worn. As shown in Figure 9A, the sternal manubrium support 3 preferably includes a sternal manubrium support member 33, a pair of left and right sternal manubrium connecting loops 32, and a sternal manubrium cushioning layer 31. The sternal manubrium connecting loops 32 are connected to the zek 57 of the elastic shoulder strap 5. As shown in Figure 9B, the sternal manubrium cushioning layer 31 preferably has a layered structure of cushioning materials, i.e., a layered structure of a first sternal manubrium cushioning layer 311, a second sternal manubrium cushioning layer 312, and a third sternal manubrium cushioning layer 313. The purposes of providing the sternal manubrium cushioning layer 31 are as follows: First, the sternal manubrium cushioning layer 31 fills the gap between the skin and the sternal manubrium support 3, thereby supporting contact of the bioelectrode 7e (see Figure 3B) supported by the sternal manubrium support 3 with the skin. Second, the sternal manubrium cushioning layer 31 transmits the force pressing the sternal manubrium support 3 against the living body to the bioelectrode 7e on the sternal manubrium. Furthermore, the sternal manubrium cushioning layer 31 deforms in response to the movement of the muscles and skin around the sternal manubrium, which is linked to arm and neck movements, thereby supporting contact of the bioelectrode 7e with the skin. For example, the sternal manubrium cushioning layer 31 may deform as shown in Figure 9D when worn. Finally, the sternal manubrium cushioning layer 31 absorbs vibrations associated with walking and running, supporting contact of the bioelectrode 7e with the skin. At this time, the stretchable shoulder straps 5 and the stretchable conductive strings 6 connected to the sternal manubrium cushioning layer 31 via the sternal manubrium support member 33 stretch and contract, thereby reducing the transmission of body movement and vibration to the bioelectrode 7e. Additionally, increasing the thickness of the sternal manubrium cushioning layer 31 increases the contact pressure of the sternal manubrium bioelectrode 7e against the skin. The contact pressure of the sternal manubrium bioelectrode 7e against the skin can also be increased by increasing the compressive stress of the cushioning material. However, excessively increasing the contact pressure can cause discomfort to the wearer, so an appropriate load must be set. Furthermore, stacking cushioning material has the following advantages.That is, as shown in Figures 26A and 26B, compared with the single cushioning material (Examples 6-2 to 6-4), the stacked cushioning materials (Examples 2, 6-5 to 6-7) exhibit a wider range of compressive stress when the compression ratio is changed. Therefore, even if the force pressing the sternal manubrium support 3 against the living body changes during application, they can respond better than a single cushioning material. According to the compressive stress measurements of the cushioning material or buffer layer described below, the sternal manubrium buffering layer 31 of Example 2 generates a compressive stress of 30 g to 100 g at a compressibility ratio of 5% to 30% and a compressive stress of 75 g to 250 g at a compressibility ratio of 30% to 50%. For example, when the diameter of the sternal manubrium buffering layer 31 is 3.5 cm, the compressive stress is 3.1 g / cm at a compressibility ratio of 5% to 30%. 2 10g / cm or more 2 At the following load, the compression ratio is 30% or more and 50% or less, and the 2 26g / cm or more 2 This corresponds to the following load:

[0041] When the load on the manubrium increases, some wearers may feel short of breath due to pressure on the throat caused by the manubrium support 3. Furthermore, even the same wearer may become more sensitive to pressure due to changes in physical condition or mental state. Therefore, for a more comfortable fit, the manubrium cushioning layer 31 preferably has a compressibility of 5% to 50% and a compressive stress of 5 g to 450 g, more preferably 15 g to 350 g, and even more preferably 30 g to 250 g. In the second embodiment of the present invention, the manubrium cushioning layer 31 is preferably used in combination with the epigastric cushioning layer 21. However, if the epigastric cushioning layer 21 is not required due to the wearer's body type, the manubrium cushioning layer 31 alone may be used.

[0042] Fig. 10A is a diagram showing an example of the configuration of the second signal transmission unit according to the second embodiment of the present invention. Fig. 10B is a diagram showing an example of the configuration of the second signal transmission unit and the epigastric buffer layer according to a preferred aspect of the second embodiment of the present invention. As shown in Fig. 10A, the second signal transmission unit 34 is preferably composed of a conductive fiber 8 and a seam tape 10. As shown in Fig. 10B, the second signal transmission unit 34 serves to connect the bioelectrode 7e on the manubrium, which is connected to the manubrium support 3, to the elastic conductive cord 6. The seam tape 10 functions as an insulator.

[0043] FIG. 11A is a perspective view of an example of a converter connecting two electrocardiographs. FIG. 11B is an exploded view showing an example of a converter connecting two electrocardiographs. For example, as shown in FIGS. 11A and 11B, a converter 70 is used to connect two electrocardiographs 90 and 91 to a harness for measuring biosignals. It is composed of conductive fiber 8, seam tape 10, a converter base 71, and a measuring instrument connector 51. The converter base 71 is preferably made of synthetic resin, nonwoven fabric, or resin-treated nonwoven fabric. For example, thick hard felt (2.5 mm thick) can be used, but is not limited to this. Furthermore, instead of the conductive fiber 8, insulating-coated wires or flat cables used in electronic devices, flexible printed circuit boards, or wiring made of insulating thin-film resin with conductive resin printed on it may also be used. The components, wiring, and their arrangement can be arbitrarily combined depending on the type and number of biosignal receiving devices connected to the converter. The shape of the transducer used in the present invention is not limited to the transducer 70 shown in FIG. 11A . Furthermore, the transducer used in the present invention may be a cable equipped with a connector that is compatible with the shapes of both the biosignal receiving device and the measuring instrument connector 51. This allows the transducer to be used in combination with the biosignal measurement harness of the present invention without changing the specifications of the existing biosignal receiving device. Examples of biosignal receiving devices include, but are not limited to, devices that measure and record electrocardiogram signals, devices that simultaneously measure and analyze electrocardiogram signals and record abnormal waveforms, devices that record or transmit electrocardiogram signals during a seizure as operated by the wearer, devices that transmit electrocardiogram signals, and devices that record electrocardiogram signals while the wearer exercises at various intensities.

[0044] The elastic waist cord 4 preferably has a length of 30 cm to 300 cm, a width of 1.0 cm to 10.0 cm, and a thickness of 0.05 cm to 0.50 cm. A length of 30 cm to 150 cm, a width of 1.0 cm to 6.0 cm, and a thickness of 0.05 cm to 0.30 cm are more preferred. The width of the elastic waist cord 4 affects the wearing comfort; for example, a wider elastic band is preferable from the viewpoint of comfort, as it disperses localized pressure associated with wearing the waist cord. Elastic bands for clothing made of polyester or nylon threads and elastic threads such as polyurethane or natural rubber are preferred as the material for the elastic waist cord 4. Elastic bands with flat cross sections, such as woven elastic bands, knitted elastic bands, and corded elastic bands, are more preferred, but are not limited to these. For example, elastic bands with round cross sections, such as round elastic bands, may also be used as the material for the elastic waist cord 4. When selecting the material for the elastic waist cord 4, it is preferable to consider the stretch rate, elongation load, feel, breathability, quick-drying properties, etc. The elastic waist cord 4 is preferably connected to the chest support 2 at an angle R3 (see Figure 3A) of 30±15° relative to the horizontal. The elastic waist cord 4 is preferably made of an elastic material that generates a stretching load of 300 g to 1200 g when stretched. For example, the stretching load of the elastic waist cord 4 is preferably 700±100 g during daily life, 400±100 g during sleep, and 1000±100 g during exercise. Specifically, the elastic waist cord 4 is made of flat elastic material S3 (width 3.0 cm, thickness 0.12 cm) as shown in Figure 23, but is not limited to this. The elongation rate when a stretching load of 300 g to 1200 g occurs varies depending on the characteristics of the elastic material used for the elastic waist cord 4. Therefore, it is preferable to determine the length of the elastic waist cord 4 by creating a relationship diagram between the wearer's body shape and the length of the elastic waist cord 4 before wearing at multiple stretching loads, as shown in Figure 18. For example, if the wearer's chest circumference (circumference at position B in Fig. 2C) is 90 cm and their waist circumference (circumference at position C in Fig. 2C) is 90 cm, the sum of the wearer's chest circumference and waist circumference is 180 cm. Using the approximation line for a stretching load of 700 g shown in Fig. 18, the length of the elastic waist cord 4 before putting on the garment is 48 cm, so the wearer can adjust each of the left and right elastic waist cords 4 to 48 cm before putting on the garment.At this time, an approximation formula can be found from the plotted approximation line, and the length of the elastic waist cord 4 before wearing can be determined by calculation. As shown in Figures 3A to 3C, the elastic waist cord 4 is provided with a front hook 43 and an eight-ring 44 as a length adjustment mechanism and a connecting mechanism, allowing the length of the elastic waist cord 4 to be changed and the stretching load to be adjusted. The front hook 43 can connect the ends of a pair of elastic waist cords 4 to each other at the front navel or front lower abdominal area. This allows the biosignal measurement harness 101 to be made in one size, allowing it to be adapted to wearers of various body types with different waist circumferences. In the present invention, the length adjustment mechanism may also serve as the connecting mechanism, or the length adjustment mechanism and the connecting mechanism may be separate entities, or they may be replaced by components with equivalent functions. The length adjustment mechanism and connecting mechanism are not limited to eight-rings, front hooks, and Z-rings. Other possible options include ring hooks, buckles, waist adjusters, strap adjusters, hook buckles, Tape-Snapper® tape, loop tape, hooks and loops, hook-and-loop fasteners, snap buttons, buttonholes, buttons, front hooks, and fish clips, either alone or in combination. The components of the length adjustment mechanism and connecting mechanism are preferably made of metal, resin-coated metal, synthetic resin, or the like. Alternatively, as shown in Figure 4B, the ends of the stretchable waist cords 4 may be connected to each other at the front navel or lower front abdomen area with a hook-and-loop fastener to adjust the length (see Figures 4A and 4B). Specifically, by arranging hook-and-loop loops 48B at predetermined intervals on the inside of one stretchable waist cord 4L and hook-and-loop hooks 48A on the outside end of the other stretchable waist cord 4R, the length can be adjusted at predetermined intervals. The predetermined intervals may be, for example, equal or proportional intervals. Regardless of which length adjustment mechanism and connecting mechanism is used, if the length of the elastic waist cord 4 is insufficient for the wearer's body type, it may be extended by connecting an independent elastic member.

[0045] The stretchable shoulder straps 5 preferably have a length of 20 cm to 200 cm, a width of 0.5 cm to 5.0 cm, and a thickness of 0.05 cm to 0.50 cm. More preferably, they have a length of 20 cm to 100 cm, a width of 0.5 cm to 3.0 cm, and a thickness of 0.05 cm to 0.30 cm. Elastic bands used for clothing, made of polyester or nylon threads and elastic threads such as polyurethane or natural rubber, are preferred. Elastic bands with flat cross sections, such as woven, knitted, or corded elastic bands, are more preferred, but are not limited to these. For example, elastic bands with round cross sections, such as round elastic bands, may also be used. When selecting the materials for the stretchable shoulder straps 5, it is preferable to consider factors such as elongation, elongation load, texture, breathability, and quick-drying properties. The stretchable shoulder straps 5 are preferably connected to the manubrium support 3 so that the angle R1 (see FIG. 9A ) relative to the horizontal is 30±20°. The stretchable shoulder straps 5 are preferably connected to the chest support 2 so that the angle R2 (see FIG. 3A) relative to the horizontal is 70±20°. The stretchable shoulder straps 5 are preferably made of elastic material that generates a stretching load of 25 g to 400 g when stretched. For example, the stretching load of the stretchable shoulder straps 5 is preferably 150±50 g during daily life, 75±50 g during sleep, and 250±50 g during exercise. Specifically, the stretchable shoulder straps 5 are made of flat elastic material S1 (width: 1.1 cm) as shown in FIG. 23 , but are not limited to this. The stretch rate when a stretching load of 25 g to 400 g occurs varies depending on the characteristics of the stretchable material used for the stretchable shoulder straps 5. Therefore, it is preferable to determine the length of the stretchable shoulder straps 5 by creating a relationship diagram between the wearer's body shape and the length of the stretchable shoulder straps 5 before wearing them, using multiple stretching loads, as shown in FIG. 19 . For example, if the wearer's shoulder length (the length of line segment A-A' in Figure 2C) is 66 cm, the length of stretchable shoulder straps 5 before wearing will be 56 cm when the approximation line for an extension load of 150 g shown in Figure 19 is used. In this case, an approximation formula can be found from the plotted approximation line, and the length of stretchable shoulder straps 5 before wearing can be determined by calculation.As shown in Figures 3A to 3C, the elastic shoulder straps 5 are provided with length adjustment mechanisms and connecting mechanisms, namely, eight-rings 56 and Z-rings 57, allowing the length of the elastic shoulder straps 5 to be adjusted to adjust the stretch load. The Z-rings 57 connect the pair of elastic shoulder straps 5 to the sternal manubrium support 3 via the sternal manubrium connecting loops 32. In the present invention, the length adjustment mechanism may also serve as the connecting mechanism, or the length adjustment mechanism and connecting mechanism may be separate entities, or may be replaced by components with equivalent functions. The length adjustment mechanism and connecting mechanism are not limited to eight-rings, Z-rings, and loop tape. For example, ring hooks, buckles, strap adjusters, hook buckles, Tape-Snapper® tape, hooks and loop fasteners, snap buttons, buttonholes, buttons, front hooks, fish clips, and the like can be used alone or in combination. The length adjustment mechanism and connecting mechanism are preferably made of metal, resin-coated metal, synthetic resin, or the like. Regardless of which length adjustment mechanism and connecting mechanism is used, if the length of the stretchable shoulder straps 5 is insufficient for the wearer's body type, they may be extended by connecting independent stretchable members.

[0046] The stretchable conductive cord 6 preferably has a length of 5.0 cm to 50.0 cm (corresponding to the line segment D-D' shown in Figure 2C), a width of 0.5 cm to 5.0 cm, and a thickness of 0.05 cm to 0.50 cm. It is more preferable that the length be 5.0 cm to 30.0 cm (corresponding to the line segment D-D' shown in Figure 2C), a width of 0.5 cm to 2.0 cm, and a thickness of 0.05 cm to 0.30 cm. The stretchable conductive cord 6 preferably has a base material made of a clothing elastic cord made of polyester, nylon, or other thread and elastic thread such as polyurethane or natural rubber, with a conductor disposed thereon. The conductor is preferably, but is not limited to, a coated electric wire. The base material for the stretchable conductive cord 6 is preferably, but is not limited to, a rubber cord with a round cross section, such as a round rubber cord, or a rubber cord with a flat cross section, such as a woven rubber cord, knitted rubber cord, or corded rubber cord. The stretchable conductive cord 6 is preferably connected to the chest support 2 at a 90° angle with respect to the horizontal direction. However, when the stretchable conductive cord 6 is detachably fastened to the first signal transmission unit 24A using conductive snap buttons, the fastening point rotates, so this is not a limitation. The stretchable conductive cord 6 is preferably a stretchable member that generates a stretching load of 75 g to 500 g when stretched and contracted, and more preferably a stretchable member that generates a stretching load of 150 g to 350 g. The stretchable conductive cord 6 preferably has an elongation rate of 150% to 300% of its length before stretching. For example, if the length of the target area when the wearer is in an upright position (the length of the line segment D-D' in FIG. 2C) is 18 cm, the length of the target area will change by ±3 cm when the wearer tilts their head forward or backward. Therefore, it is preferable to determine the length and elongation rate of the stretchable conductive cord 6 taking into account changes in posture. As shown in FIG. 3B, if the stretchable conductive cord 6 uses a stretchable member to which the electric wire 61 is fastened in a wavy shape, it can follow the expansion and contraction of the target area due to changes in posture. For example, but not limited to, an electric wire S2 (length 16.0 cm, width 1.2 cm, thickness 0.15 cm, electric wire cycle 2 cycles / cm, elongation rate 200%) can be used as the stretchable conductive cord 6. As an alternative to the electric wire S2, a stretchable wiring may be used in which conductivity is imparted to a stretchable base material and a stretchable conductive film is formed.Alternatively, instead of fixing a conductor to the stretchable substrate, a cable equipped with a connector and lead wires for connecting the first and second signal transmission units may be used in conjunction with the stretchable substrate to achieve stretchability and conductivity. This allows the stretchable substrate to have a length adjustment mechanism and a connecting mechanism. The length adjustment mechanism and connecting mechanism are not limited to eight-rings, Z-rings, and loop tape, but may also include, for example, ring rings, buckles, strap adjusters, hook buckles, Tape-Snapper® tape, hooks and loops, hook-and-loop fasteners, snap buttons, buttonholes, buttons, front hooks, and fish clips, either alone or in combination. Metal, resin-coated metal, synthetic resin, and the like are preferred materials for the length adjustment mechanism and connecting mechanism. In the present invention, the length adjustment mechanism may also function as the connecting mechanism, or the length adjustment mechanism and connecting mechanism may be separate entities, or may be replaced by a component with equivalent functionality.

[0047] As a method for adjusting the length of the stretchable conductive cord 6, the length may be shortened by folding a part of the stretchable conductive cord 6 and fixing it with a fish clip or the like. Alternatively, the length may be extended by connecting an extension stretchable conductive cord (not shown) equipped with a conductive snap button or the like to the stretchable conductive cord 6. In this case, it is preferable that the length of the extension stretchable conductive cord is 2.0 cm or more and 10.0 cm or less, and that conductive connectors such as conductive snap buttons are provided on both ends of the extension stretchable conductive cord.

[0048] The bioelectrode 7 is preferably a flexible bioelectrode containing a conductive polymer, conductive carbon black, graphene, or metal microparticles as a component, but is not limited thereto. For example, a bioelectrode may be used that is a conductive fiber structure impregnated with a conductive material, with the conductive material being supported on the surfaces and between the individual fibers constituting the conductive fiber structure. The conductive material is not particularly limited as long as it is a conductive compound. Examples of the conductive material include conductive polymers such as PEDOT / PSS (poly(3,4-ethylenedioxythiophene) / polystyrene sulfonate), carbon-based conductive materials such as carbon black, and conductive materials containing metal microparticles. When conductive carbon black, graphene, metal microparticles, etc. are used as the conductive material, polymer adhesives such as urethane-based polycarbonate and urethane-based polyether can be used. Examples of the conductive fiber structure include fabrics such as knitted fabrics, woven fabrics, and nonwoven fabrics, as well as string-like materials. Knitted fabrics or woven fabrics are preferred. The conductive surface of the bioelectrode 7 that comes into contact with the wearer's skin is preferably non-adhesive. However, even if the bioelectrode 7 has adhesive on its conductive surface, the bioelectrode 7 can be used in combination with the biosignal measurement harness 101. Furthermore, the bioelectrode 7 is not limited to a resistively coupled electrode that is used in direct contact with the skin, but a capacitively coupled electrode that is used without direct contact with the skin can also be used in combination with the biosignal measurement harness 101. The shape of the bioelectrode 7 is preferably circular with a diameter of 2.0 cm to 5.0 cm, but is not limited thereto as long as it can detect biosignals. For example, as shown in FIG. 3B , the bioelectrode 7 may be detachably electrically connected to the first signal transmission unit 24A using an electrode connector 52. In this case, if the thickness of the electrode connector 52 creates a step on the back surface of the chest support 2A, causing pain or discomfort to the wearer, it is preferable to provide a step cushioning material 27 to reduce the step. Alternatively, the bioelectrode 7 may be non-detachably adhered to the chest support 2A, and the bioelectrode 7 may be electrically connected to the first signal transmission unit 24A using the electrode connector 52.This increases the convenience for the wearer by allowing the biosignal measurement harness 101 to be washed without removing the bioelectrodes 7. Furthermore, the bioelectrodes 7 may be placed on the track (back surface) of the elastic waist cord 4 using a member required for electrical connection with the first signal transmission unit 24A.

[0049] The elongation loads (g) W1, W2, W3 of the stretchable shoulder straps 5, stretchable conductive straps 6, and stretchable waist strap 4, respectively, the angle R1 (°) at which the stretchable shoulder straps 5 connect to the manubrium support 3, the angle R2 (°) at which the stretchable shoulder straps 5 connect to the thoracic support 2, and the angle R3 (°) at which the stretchable waist strap 4 connects to the thoracic support 2 are preferably designed to satisfy the following relationship: A = W1 x sin(R1) x 2 - W2 B = W1 x sin(R2) x 2 + W2 - W3 x sin(R3) x 2 - 150g < A < 150g - 300g < B < 300g

[0050] For example, if W1 = 150, W2 = 250, W3 = 700, R1 = 30, R2 = 70, and R3 = 30 for the stretchable shoulder straps 5, stretchable conductive straps 6, and stretchable waist strap 4, then A = -100 and B = -168. However, because the angles and elongation rates of the stretchable waist strap 4, stretchable shoulder straps 5, and stretchable conductive straps 6 change depending on the wearer's physique, shape, and body movements, the above conditions may not be met when the device is worn.

[0051] The material of the conductive fiber 8 is not particularly limited, and known conductive fibers can be used. Examples of materials that can be used for the conductive fiber 8 include, but are not limited to, metal-plated fibers, conductive polymer fibers, metal fibers, carbon fibers, and composite fibers. The conductive fiber 8 is not limited to a single type, and two or more types may be used in combination. The electrical resistance of the conductive fiber 8 is preferably 10 Ω / cm or less, more preferably 1 Ω / cm or less, and even more preferably 0.1 Ω / cm or less, in terms of linear resistance. Examples of metal-plated fibers include synthetic fibers whose surfaces are coated with a metal. Examples of such metals include gold, silver, copper, stainless steel, aluminum, and the like, as well as alloys containing at least one of these metals. Examples of synthetic fibers used for the conductive fiber 8 include, but are not limited to, polyamide-based synthetic fibers such as nylon and polyester-based synthetic fibers such as polyester. Examples of composite fibers used for the conductive fiber 8 include, but are not limited to, fibers in which carbon black is compositely arranged along the length of the fiber in a portion of the core or sheath of polyester or nylon. Furthermore, instead of the conductive fiber 8, an insulating coated wire or flat cable used in electronic devices, a flexible printed circuit board, or wiring in which a conductive resin is printed on an insulating thin film resin may be used.

[0052] In this second embodiment, the epigastric buffer layer 21 may have a laminated structure, for example, as shown in FIG. 6C , consisting of a first layer 211 and a second layer 212 of different materials. However, the number of layers and configuration of the epigastric buffer layer 21 are not limited to this. The shape of the epigastric buffer layer 21 is preferably a polygonal shape, such as a triangle, rectangle, pentagon, or hexagon, a circle, or a combination of these shapes. Furthermore, the top and bottom surfaces of the epigastric buffer layer 21 may be parallel or non-parallel, and may be flat or curved. The areas of the top and bottom surfaces may be the same or different. The buffer material constituting the epigastric buffer layer 21 may be a single-material buffer material or a composite-material buffer material. The epigastric buffer layer 21 preferably has a thickness of 0.5 cm to 5.0 cm at a compression rate of 0% and a diameter of 1.0 cm to 8.0 cm. The epigastric buffer layer 21 absorbs the positive pressure acting on the body generated by the chest support 2 and transmits that pressure to the epigastric bioelectrode 7c. However, because the shape of the wearer's epigastric area and the gap between the chest support 2 and the skin vary depending on the wearer's body type and build, it is preferable to adjust the size and shape of the epigastric buffer layer 21 to suit the wearer. Examples of materials that can be used for the epigastric buffer layer 21 include, but are not limited to, cushioning materials, foam, air cushions, and gels. The epigastric buffer layer 21 is formed by stacking cushioning materials with different compressive stresses, and has different compressive stresses on one side and the other side. For example, the compressive stress on the stretchable portion 23A side (rear side) is preferably smaller than the compressive stress on the non-stretchable portion 25 side (front side). It is also preferable for the cushioning material on the stretchable portion 23A side (rear side) to have a compressive hardness of 50 g / cm at 25% compression as specified in JIS K6767. ２A cushioning material having a compressive hardness of 0.1 to 1.0 g / cm or less is preferred, and one having vibration-damping properties is preferable. The cushioning material on the non-stretchable portion 25 side (surface), such as a non-stretchable fabric, is preferably harder than the cushioning material on the stretchable portion 23A side (back surface) at 25% compression, and this cushioning material can be used as a support member. Furthermore, between the cushioning material on the stretchable portion 23A side (back surface) and the cushioning material on the non-stretchable portion 25 side (surface), a cushioning layer with a different compressive stress may be used to change the compressive stress characteristics of the cushioning layer, or the same cushioning material may be used to increase the thickness of the cushioning layer. When cushioning materials with different compressive stresses are stacked, the epigastric cushioning layer 21 exhibits compression characteristics due to the compressive stress of each cushioning material. In Example 2 according to the present embodiment 2, cushioning material F1 (material: ethylene propylene diene copolymer foam, compressive hardness of 40 g / cm at 25% compression as specified in JIS K6767) was used as the first layer epigastric cushioning material 211 on the stretchable portion 23A side (back surface). 2 , thickness 15 mm), and a cushioning material F2 (material: polyolefin foam, apparent density 130±20 kg / m as specified in JIS K6767) as the second layer epigastrium cushioning material 212 on the non-stretchable portion 25 side (surface). 3 25% compression hardness as specified in JIS K6767: 1428±510 g / cm 2 , 5 mm) formed into a 4.5 cm diameter buffer layer can be used, but is not limited to this.

[0053] As shown in FIG. 3C , the epigastric pocket 22 functions to accommodate the epigastric cushioning layer 21 in the chest support 2. As described above, the size and shape of the epigastric cushioning layer 21 are preferably customizable to suit the wearer, and therefore the epigastric pocket 22 is preferably large enough to accommodate the epigastric cushioning layer 21. The epigastric pocket 22 may be made of the same material as the stretchable portion 23A, but is not limited to this. The epigastric pocket 22 may be formed by folding the fabric of the stretchable portion 23A. The skin side of the epigastric pocket 22 is preferably stretchable and thin so that it can easily deform to fit the surface shape of the epigastric region. When accommodating the epigastric cushioning layer 21 in the epigastric pocket 22, it is preferable to detachably fasten it using a mechanical fastener or the like, but this is not limited to this. The opening of the epigastric pocket 22 may be left open or may be openable and closable.

[0054] The material for the stretchable portion 23A is preferably selected taking into consideration factors such as thinness, lightness, texture, breathability, stretchability, quick-drying properties, and resistance to unraveling. Specifically, highly stretchable fabrics such as two-way tricot, power net, and smooth knit, which are commonly used in underwear, are used for the stretchable portion 23A, but the stretchable portion 23A is not limited to these. The stretchable portion 23A may be made of polyester-based synthetic fibers such as polyester, polyamide-based synthetic fibers such as nylon, polyurethane, or other materials, either alone or in any combination, but is not limited to these. Furthermore, natural materials such as cotton and linen can also be used as the fabric material. The stretchable shoulder straps 5 and the stretchable waist strap 4 are preferably connected to the stretchable portion 23A by sewing, bonding, welding, or a combination thereof. It is preferable to layer the stretchable shoulder straps 5 and the stretchable waist strap 4 on the surface of the stretchable portion 23A in this order. When sewing, it is preferable to sew from the back surface that comes into contact with the skin so that seams such as welded seams do not directly touch the skin. In the case of adhesion or welding, it is preferable to adhere or weld in a planar, mesh, or dotted pattern. The shape of the stretchable portion 23A can be designed to be rectangular, trapezoidal, circular, or a combination of these shapes.

[0055] The material of the non-stretchable portion 25 is preferably selected taking into consideration factors such as thinness, lightness, texture, breathability, quick-drying properties, and resistance to unraveling. Examples of materials for the non-stretchable portion 25 include polyester synthetic fibers and cotton, either alone or in any combination. For example, 100% polyester interlining can be used for the non-stretchable portion 25, but the material of the non-stretchable portion 25 is not limited to this. The non-stretchable portion 25 is the location where the tensile stress of the elastic cord connected to the non-stretchable portion 25 is transmitted, and is preferably non-stretchable so that it does not easily deform due to tensile stress. Furthermore, the non-stretchable portion 25 of the chest electrode support supports the multiple bioelectrodes, the measurement instrument connector, and the first signal transmission unit, thereby advantageously maintaining a constant spacing between the multiple bioelectrodes on the chest electrode support.

[0056] The step cushioning material 27 (see FIG. 3B ) is sufficient to cushion the thickness of the electrode connector 52, and preferably has a thickness of 0.3 cm to 1.0 cm. Examples of materials that can be used for the step cushioning material 27 include, but are not limited to, foams such as polyurethane and polyolefin. The step cushioning material 27 may be a single layer, or may be a layer of cushioning materials such as the epigastric cushioning layer 21 and the manubrium cushioning layer 31.

[0057] In this second embodiment, the sternal manubrium cushioning layer 31 may have a laminated structure, as shown in FIG. 9B , consisting of a first sternal manubrium cushioning layer 311, a second sternal manubrium cushioning layer 312, and a third sternal manubrium cushioning layer 313 made of different materials. However, the number of layers and configuration of the sternal manubrium cushioning layer 31 are not limited to this. The shape of the sternal manubrium cushioning layer 31 is preferably a polygon (e.g., triangular, rectangular, pentagonal, or hexagonal), a circle, or a combination thereof. The top and bottom surfaces of the sternal manubrium cushioning layer 31 may be parallel or non-parallel, and may be flat or curved. The areas of the top and bottom surfaces may be the same or different. The cushioning material constituting the sternal manubrium cushioning layer 31 may be a single-material or composite-material cushioning material. The sternal manubrium cushioning layer 31 preferably has a thickness of 0.5 cm to 5.0 cm at 0% compressibility and a diameter of 1.0 cm to 8.0 cm. The sternal manubrium cushioning layer 31 absorbs the force pressing the sternal manubrium support 3 against the living body and transmits that pressure to the bioelectrode 7e on the sternal manubrium. However, because the shape of the wearer's sternal manubrium and the gap between the sternal manubrium support 3 and the skin vary depending on the wearer's body type and build, it is preferable to adjust the size and shape of the sternal manubrium cushioning layer 31 to suit the wearer. Examples of materials that can be used for the sternal manubrium cushioning layer 31 include, but are not limited to, cushioning materials, foam, air cushions, and gels. The sternal manubrium cushioning layer 31 is formed by laminating cushioning materials with different compressive stresses, and has different compressive stresses on one side and the other side. For example, it is preferable that the compressive stress on the bioelectrode 7e side (back side) be smaller than the compressive stress on the opposite side (front side). The cushioning material on the bioelectrode 7e side (back side) is preferably a cushioning material with a hardness of 20N ("N" here means Newton (unit)) to 55N as specified in JIS K6400-2, and preferably has vibration-absorbing properties. The cushioning material of the third layer manubrium cushioning material 313 on the opposite side (front side) is preferably a cushioning material harder than the cushioning material on the bioelectrode 7e side (back side), and can be used as a support member.Furthermore, it is preferable to use a buffer layer with a different compressive stress between the buffer material on the bioelectrode 7e side (back side) and the buffer material on the opposite side (front side) to change the compressive stress characteristics of the buffer layer, or to use the same buffer material to increase the thickness of the buffer layer. When buffer materials with different compressive stresses are stacked, the sternal manubrium buffer layer 31 exhibits compressive characteristics due to the compressive stress of each buffer material. For example, in Example 6-6 of this embodiment 2, the first layer sternal manubrium buffer 311 is made of buffer material F5 (material: polyurethane foam, apparent density 20±3 kg / m as specified in JIS K7222). 3 , hardness 30±10N specified in JIS K6400-2, specific gravity 0.02g / cm 3 , thickness 5 mm), and as the second layer sternal manubrium cushioning material 312, cushioning material F4 (material: polyether-based polyurethane foam, apparent density 35±3 kg / m as specified in JIS K7222) 3 , hardness specified in JIS K6400-2: 125±30N, specific gravity: 0.035g / cm 3 The third layer of sternal manubrium cushioning material 313 may be a cushioning layer formed by stacking cushioning material F6 (material: ethylene vinyl acetate copolymer, thickness 4 mm) in order, and molded to a diameter of 3.5 cm, but is not limited to this.

[0058] Some wearers have a concave central chest, similar to pectus excavatum. Therefore, the shape and size of the epigastric cushioning layer 21 and the manubrium cushioning layer 31 are not limited to those described above, and can be changed as desired to suit the wearer's body shape.

[0059] The material of the manubrium connecting loop 32 is preferably the same as that of the elastic shoulder strap 5, but is not limited to this. The manubrium connecting loop 32 is preferably fixed at an angle R1 of 30±20° where it connects to the manubrium support member 33 of the elastic shoulder strap 5, and is preferably fixed to the manubrium support member 33 by, for example, sewing, adhesive, or welding.

[0060] Examples of materials for the manubrium support member 33 include, but are not limited to, synthetic leather, artificial leather, and nonwoven fabric. The shape of the manubrium support member 33 is preferably a polygon such as a triangle, square, pentagon, or hexagon, or a circle, with a hexagon or circle being more preferred. The size of the manubrium support member 33 is preferably 2.0 cm to 8.0 cm wide, 2.0 cm to 8.0 cm high, and 0.05 cm to 0.3 cm thick.

[0061] 10A, the second signal transmission unit 34 is composed of a conductive fiber 8 and a seam tape 10. The conductive fiber 8 is connected to the conductive connector 53 at the inner center, center, vertical center, or center of gravity of the sternal manubrium support member 33, and is connected to the electrode connector 52 at the center of the first-layer sternal manubrium cushioning material 311. The conductive fiber 8 is preferably waterproofed and insulated by the seam tape 10. Instead of the conductive fiber 8, an insulating-coated wire or flat cable used in electronic devices, a flexible printed circuit board, or wiring made of insulating thin-film resin with a conductive resin printed on it may be used.

[0062] As the measuring instrument connector 51, it is preferable to use a snap button or connector hook, which is used in, for example, a biosignal receiving device such as a long-term electrocardiogram recorder, medical equipment, etc. and has conductivity suitable for measuring biosignals. The measuring instrument connector 51 can be selected from a combination of a tenon and a spring, or a combination of a tenon and a spring.

[0063] It is preferable to use conductive snap buttons or connector hooks, which are used in medical materials and clothing, as the electrode connector 52 and the conductive connector 53. The electrode connector 52 and the conductive connector 53 can be selected from a combination of a head and a spring, or a combination of a spring and a clamp.

[0064] In the biosignal measurement harness of the present invention, instead of bioelectrodes for electrocardiogram measurement, sensors for measuring bioinformation such as body surface temperature, blood oxygen saturation, respiratory rate, and other biosounds can be used as biosignal measurement sensors, and these can be used in combination with the bioelectrodes. However, the biosignal measurement sensors to be combined are not limited to these, and a biosignal receiving device that is compatible with the biosignal measurement sensor to be combined can also be selected as desired.

[0065] The most common electrocardiogram lead method used in medical institutions is the standard 12-lead method, which uses 10 electrodes and six chest leads (leads I, II, III, and aV). R , aV L , aV FElectrocardiograms are typically performed using a 12-lead electrocardiogram (12-lead) and six limb leads (V1, V2, V3, V4, V5, and V6). On the other hand, long-term electrocardiogram recording devices, such as patch electrocardiographs, typically use two electrodes (excluding the reference electrode) to perform electrocardiograms using bipolar leads, such as the CM5 lead, which is made up of a positive electrode on the rib near V5 and a negative electrode on the manubrium; the CC5 lead, which is made up of a positive electrode on V5 and a negative electrode on V5R; or the NASA lead, which is made up of a positive electrode on the xiphoid process of the sternum and a negative electrode on the manubrium. Standard 12-lead electrocardiograms, which are performed at rest in medical institutions and record electrocardiograms for several minutes, allow for multifaceted observation of the heart due to their large number of leads, providing useful information for diagnosing abnormal arrhythmias and ischemic heart disease. 12-lead Holter electrocardiograms, which can record electrocardiograms continuously for up to 48 hours, are also known. In contrast, patch electrocardiographs record electrocardiograms for 7 to 14 days during daily life. By recording for a long period of time instead of limiting the number of leads to one, it is superior in detecting rare abnormal arrhythmias. Thus, the number of leads and recording time vary depending on the device, and comfort, data volume, and analysis load are also not uniform. On the other hand, several methods have been reported for deriving a 12-lead ECG using fewer electrodes than the standard 12-lead ECG. For example, in the EASI lead reported by Dower et al., an ECG is recorded using five electrodes: an E electrode placed at the same height as the fifth intercostal space below the sternum, an A electrode placed in the fifth intercostal space on the left mid-axillary line, an S electrode placed above the sternum, an I electrode placed in the fifth intercostal space on the right mid-axillary line, and a reference electrode. A 12-lead ECG can be derived from the resulting ECGs of leads ES, AS, and AI using conversion coefficients. Furthermore, Field et al. reported a method for deriving a 12-lead ECG using three posterior leads (V7, V8, V9) and three right leads V1. 3R , V 4R , V 5RThe derivation of EASI leads (1), three Frank orthogonal leads (X, Y, Z), and three vascular-specific leads (LAD, LCx, RCA) has been reported. The function of recording electrocardiograms using EASI leads is implemented in devices for continuous bedside monitoring and small devices for minute-by-minute monitoring in combination with adhesive bioelectrodes during daily life. However, a method for comfortably measuring electrocardiograms continuously over long periods of time in daily life is unknown. The biosignal measurement harness according to the second embodiment supports the S electrode of the five EASI leads with the manubrium support 3 and the E, A, I, and reference electrodes with the chest support 2, thereby providing a method for comfortably measuring EASI leads over long periods of time in daily life. However, the leads applicable to the biosignal measurement harness according to the second embodiment are not limited to EASI leads. When recording using CM5 or NASA leads, the negative electrode on the manubrium can be supported by the manubrium support 3, and the positive electrode on the rib near V5 or the positive electrode on the xiphoid process of the sternum can be supported by the chest support 2. Furthermore, when recording using CC5 leads, the positive electrode on V5 and the positive electrode on V 5R The positive and negative electrodes can be supported by the chest support 2. Therefore, these leads can be combined arbitrarily to measure an electrocardiogram.

[0066] The biosignal measurement harness according to the second embodiment may have scales indicating adjustment positions on the stretchable shoulder straps 5 and the stretchable waist strap 4 to facilitate length adjustment by the wearer. For example, scales may be displayed every 1 cm, or standard adjustment positions for sizes S, M, and L may be displayed. Specifically, if the standard shoulder lengths for the stretchable shoulder straps 5 are defined as 48 cm for size S, 58 cm for size M, and 68 cm for size L, the lengths of the stretchable shoulder straps 5 before wearing can be set to 43 cm, 50 cm, and 58 cm, respectively, according to FIG. 19 . By drawing lines on the stretchable shoulder straps 5 at these positions to indicate S, M, and L, respectively, the wearer can adjust the length of the stretchable shoulder straps 5 according to the displayed scales. Furthermore, if the standard sum of the wearer's chest circumference and waist circumference for the elastic waist cord 4 is set to 140 cm for size S, 180 cm for size M, and 220 cm for size L, then according to Figure 18, the length of one side of the elastic waist cord 4 before wearing the garment can be set to 40 cm, 49 cm, or 58 cm, respectively. By drawing lines on the elastic waist cord 4 at these positions and displaying S, M, or L, respectively, the wearer can adjust the length of the elastic waist cord 4 according to the display. With these adjustment position indications, the wearer can freely adjust the lengths of the elastic shoulder straps 5 and elastic waist cord 4 without using the relationship diagrams exemplified in Figures 18 and 19.

[0067] (Embodiment 3) A biosignal measurement harness according to embodiment 3 of the present invention will be described. FIGS. 12A to 12D are diagrams showing an example of how the biosignal measurement harness according to embodiment 3 of the present invention is worn. As shown in FIGS. 12A to 12D, the biosignal measurement harness 104 according to embodiment 3 includes a subclavian fossa support 11 instead of the above-described sternal manubrium support 3. In this biosignal measurement harness 104, the stretchable conductive cord 6 is extended by an extension stretchable conductive cord 62 having a conductive connector 53. However, in the biosignal measurement harness 104, the extension stretchable conductive cord 62 may not be used, and the stretchable conductive cord 6 itself may be lengthened. An elastic shoulder strap 5L connected to the left end of the chest support 2 extends to the region between the scapular line and the axillary line and connects to the subclavian fossa support 11 via the left shoulder. Furthermore, the elastic shoulder strap 5R connected to the right end of the chest support 2 extends diagonally across the posterior midline and connects to the subclavian fossa support 11 via the left shoulder near the neck. The pair of elastic waist straps 4 pass along the sides of the body, cross or connect with each other in a sliding manner at the lower back, and then pass along the sides of the body again and connect in the anterior navel or anterior lower abdominal area, thereby securing the chest support 2A to the human chest. In this way, the two elastic shoulder straps 5L and 5R both pass over the left shoulder, the same as the subclavian fossa support. Note that in cases where the wearer's heart is dextrocardia, which is opposite to normal, the subclavian fossa support 11 may be moved to the right side, and the two elastic shoulder straps 5L and 5R may be worn so that they both pass over the right shoulder. In this case, to reduce myoelectric noise, it is preferable to place the subclavian fossa support 11 in an area of ​​the subclavian fossa where there is less muscle, but this is not a limitation. The infraclavicular fossa support 11 preferably has an infraclavicular fossa cushioning layer (not shown). This infraclavicular fossa cushioning layer has the same structure as the manubrium cushioning layer 31 of the manubrium support 3 (see Figures 9A to 9D), and plays the same role for the infraclavicular fossa support 11 as the manubrium cushioning layer 31 plays for the manubrium support 3. The above structure and attachment mechanism can avoid discomfort caused by compression of the manubrium.

[0068] A biosignal measurement harness according to a fourth embodiment of the present invention will now be described. Figures 13A to 13D are diagrams showing an example of how the biosignal measurement harness according to the fourth embodiment of the present invention is worn. As shown in Figures 13A to 13D, the biosignal measurement harness 105 according to the fourth embodiment includes, instead of the chest support member 2 described above, a lateral chest support member 12 that supports bioelectrodes at positions that contact the left anterior chest, left side, and left posterior chest of the human body, and further includes a subclavian fossa support member 11 instead of the manubrium support member 3 described above. In this biosignal measurement harness 105, an elastic shoulder strap 5R connected to the right end of the lateral chest support member 12 passes over the right side of the body, is pulled out to the back, extends diagonally across the posterior midline, passes over the left shoulder on the neck side, and is connected to the subclavian fossa support member 11. Furthermore, the elastic shoulder strap 5L connected to the left end of the lateral thoracic support 12 passes over the right side of the body, is pulled to the front, extends diagonally across the anterior midline, and connects to the subclavian fossa support 11. The elastic conductive string 6 extends over the left side of the body and connects to the subclavian fossa support 11 at the infraclavicular fossa. The left and right (front and back in the figure) elastic waist straps 4 cross or connect to each other in a sliding manner at the sides of the body, and then pass over the front and lower back and connect at the opposite side of the body, securing the lateral thoracic support 12 to the lateral thoracic region of the human body. In the case of a dextrocardia, the device can be worn with the left and right sides reversed. With the above configuration and wearing mechanism, multiple bioelectrodes 7 can be placed on the wearer's subclavian fossa, left anterior chest, lateral chest, and back. The number and position of the bioelectrodes 7, the shape of the first signal transmission unit 24A, the number and position of the measuring instrument connectors 51 for connecting the biosignal receiving device, and the shape of the lateral thoracic support 12 can be modified as needed depending on the purpose of biosignal measurement. The infraclavicular fossa support 11 preferably has an infraclavicular fossa cushioning layer (not shown). This infraclavicular fossa cushioning layer has the same structure as the manubrium cushioning layer 31 of the manubrium support 3 (see Figures 9A to 9D ), and serves the same function for the infraclavicular fossa support 11 as the manubrium cushioning layer 31 does for the manubrium support 3.

[0069] (Embodiment 5) A biosignal measurement harness 106 according to embodiment 5 of the present invention will be described. FIG. 14A is a perspective view of an example of the configuration of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 14B is an enlarged view of a connecting portion of a sternal manubrium support of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 14B shows an enlarged view of a region K1 of the sternal manubrium support 3 enclosed by a dashed circle in the biosignal measurement harness 106 shown in FIG. 14A. FIG. 14C is an enlarged view of a connecting portion of an elastic portion of the biosignal measurement harness according to embodiment 5 of the present invention. FIG. 14C shows an enlarged view of a region K2 of the elastic portion 23C enclosed by a dashed circle in the biosignal measurement harness 106 shown in FIG. 14A. As shown in FIGS. 14A to 14C, the biosignal measurement harness 106 according to embodiment 5 has a chest support 2C instead of the chest support 2A described above, and further has an elastic portion 23C that covers the chest. The chest support 2C is similar to the chest support 2A described above, except that it is positioned on the stretchable section 23C. The stretchable conductive cord 6 enters the back of the stretchable section 23C through a slit (the position of line F in Figure 14A). The stretchable section 23C has stretchable extension shoulder straps 63A at the left and right upper ends, connecting the stretchable section 23C to the manubrium support 3. The stretchable extension shoulder straps 63A preferably have a Z-ring 46 (see Figure 14B) at one end and a loop 58 (see Figure 14C) at the other end. As shown in Figure 14B, the Z-ring 46 preferably connects to the manubrium connecting loop 32 of the manubrium support 3. As shown in Figure 14C, the Z-ring 57 of the stretchable shoulder strap 5 preferably connects to the loop 58. The stretchable section 23C preferably has a chest pocket 14 for accommodating a bra pad 13.

[0070] (Embodiment 6) A biosignal measurement harness according to embodiment 6 of the present invention will be described. FIG. 15 is a diagram showing a configuration example of a chest cover of the biosignal measurement harness according to embodiment 6 of the present invention, viewed from the front. The biosignal measurement harness according to embodiment 6 includes a detachable chest cover 15 (see FIG. 15 ) in addition to the biosignal measurement harness 101 of embodiment 2 described above. As shown in FIG. 15 , the chest cover 15 preferably includes multiple chest cover connectors 54 and extension stretchable shoulder straps 63B connecting the stretchable shoulder straps 5 to the sternal manubrium support 3. The extension stretchable shoulder straps 63B have a zet loop 46 at one end and a loop 58 at the other end, and are secured to the chest cover 15. In embodiment 6, it is preferable to add multiple chest cover connectors (not shown) to the chest support 2 of embodiment 2 described above, thereby connecting the chest cover connectors, including the chest cover connectors 54 of the chest cover 15, to the chest support 2. The chest cover 15 preferably has a chest pocket 14 for accommodating the bra pads 13. The connecting mechanism for connecting the chest cover 15 to the chest support member 2 is not limited to a z-ring or a loop, but may also be, for example, Tape-Snapper (registered trademark) tape, a hook and loop fastener, a snap button, a buttonhole, a button, a fish clip, or the like.

[0071] Next, specific examples of the harness for measuring biological signals according to the present invention will be described in detail. Note that the harness for measuring biological signals according to the present invention is not limited to the examples shown below.

[0072] Example 1 In Example 1, the biosignal measurement harness 100 shown in Figures 1A to 1C was produced. First, conductive fibers 8 were arranged on the adhesive surface of a molded seam tape 10, and another seam tape 10 was placed on top of it and thermally bonded. Next, a measuring instrument connector 51 was attached to the conductive fibers 8 to obtain a first signal transmission section 24. Then, the first signal transmission section 24 (which also served as a non-stretchable section) was placed on the stretchable section 23 and thermally bonded, and then an electrode connector 52 for connecting a bioelectrode 7 to the first signal transmission section 24 was attached to complete the chest support body 2. Next, a pair of stretchable waist cords 4 (2.0 cm wide) with front hooks 43 and eight-ring loops 44 attached were placed on top of each other and sewn to the left and right ends of the seam tape 10 and the stretchable section 23 on the surface of the chest support body 2, respectively, to obtain the biosignal measurement harness 100.

[0073] Example 2 In Example 2, a biosignal measurement harness 101 shown in Figures 2A to 2C was produced. For the chest support 2, first, the conductive fiber 8 and the wire 61 of the stretchable conductive cord 6 (1.2 cm wide) were aligned on the adhesive surface of the molded seam tape 10, and another piece of seam tape 10 was then placed on top of it and thermally bonded. Next, a measuring instrument connector 51 was attached to the conductive fiber 8 to form a first signal transmission unit 24A. The stretchable portion 23A was partially folded to form the epigastric pocket 22, after which the first signal transmission unit 24A and the non-stretchable portion 25 were sequentially placed on top of it and thermally bonded. Furthermore, an electrode connector 52 for connecting the bioelectrode 7 to the first signal transmission unit 24A was attached to form the chest support 2A (see Figures 3A to 3C and 7). Next, a pair of stretchable shoulder straps 5 (1.1 cm wide) with Z-rings 57 and Eight-rings 56 attached were overlapped and sewn to the left and right ends of the stretchable section 23A on the surface of the chest support 2A. Next, a stretchable waist strap 4 (2.0 cm wide) with a front hook 43 and Eight-rings 44 attached was overlapped and sewn to the left and right ends of the stretchable section 23A and the non-stretchable section 25. For the sternal manubrium support 3, a sternal manubrium connecting loop 32 (1.1 cm wide) was first sewn to the sternal manubrium support member 33 (made of polyurethane). Next, the sternal manubrium support member 33 was connected to one end of the conductive fiber 8 sandwiched between the molded seam tape 10 using a conductive connector 53. The other end of the conductive fiber 8 is connected to a first layer of the manubrium cushioning material 311 (cushioning material F4, material: polyether-based polyurethane foam, apparent density 35±3 kg / m as specified in JIS K7222) by an electrode connector 52. 3 , hardness specified in JIS K6400-2: 125±30N, specific gravity: 0.035g / cm 3 , thickness 5 mm) was connected to obtain the second signal transmission section 34. Next, the second layer manubrium cushioning material 312 (cushioning material F3, material: polyurethane foam, apparent density 20±3 kg / m as specified in JIS K7222) was connected to the second layer manubrium cushioning material 312. 3 , hardness 30±10N specified in JIS K6400-2, specific gravity 0.02g / cm 3The epigastric cushioning layer 21 was fabricated by laminating a first layer epigastric cushioning material 211 (buffer material F1, ethylene propylene diene copolymer foam, compression hardness 40 g / cm at 25% compression as specified in JIS K6767) and a third layer sternal manubrium cushioning material 313 (buffer material F6, material: ethylene vinyl acetate copolymer, thickness 4 mm) to a diameter of 3.5 cm. In this way, a buffer layer was obtained using these buffer materials. A hole with a diameter of 1 cm was drilled in the center of the obtained buffer layer, and the second signal transmission unit 34 was passed through this hole. The buffer materials were then bonded together to produce the sternal manubrium support 3 (see Figures 9A to 9D). The epigastric cushioning layer 21 was fabricated by laminating a first layer epigastric cushioning material 211 (buffer material F1, ethylene propylene diene copolymer foam, compression hardness 40 g / cm at 25% compression as specified in JIS K6767). 2 , thickness 15 mm) and a second layer epigastric cushioning material 212 (cushioning material F2, material: polyolefin foam, apparent density 130±20 kg / m as specified in JIS K6767). 3 25% compression hardness as specified in JIS K6767: 1428±510 g / cm 2 , 5 mm thick) was adhered to the chest support 2, and then processed into a circle with a diameter of 4.5 cm (see Figures 6A to 6D). Finally, the epigastric cushioning layer 21 was placed in the epigastric pocket 22 of the chest support 2, and the elastic shoulder straps 5, elastic conductive straps 6, and sternal manubrium support 3 were connected to obtain the harness 101 for measuring biological signals.

[0074] Example 3 In Example 3, the biosignal measurement harness 102 shown in Figures 4A and 4B was produced. Unlike Example 2, the biosignal measurement harness 102 of Example 3 used 3.0 cm wide flat elastic bands S3 for the stretchable waist cords 4R and 4L. Furthermore, a hook-and-loop fastener 48A was sewn to the rear surface of the end of the stretchable waist cord 4R, and five hook-and-loop fastener loops 48B were sewn to the front surface of the end of the stretchable waist cord 4L at equal intervals of 4 cm from the end. Except for the above, the biosignal measurement harness 102 was produced in the same manner as in Example 2, and thus obtained.

[0075] Example 4 In Example 4, a biosignal measurement harness 103 shown in Figures 5A and 5B was manufactured. Unlike Example 2, the biosignal measurement harness 103 of Example 4 used a non-slip material 72 on the back surface of the stretchable portion 23B, and the bioelectrode 7 was thermally bonded to it. Furthermore, a first signal transmission unit 24B with a different electrode arrangement than Example 2 was used as a substitute for the non-stretchable portion. Furthermore, a vertically penetrating epigastric pocket 22A for accommodating the epigastric buffer layer 21 was provided on the back surface of the measurement instrument connector 51. Furthermore, auxiliary stretchable members 26 (5.0 cm wide) were sewn onto the left and right ends of the first signal transmission unit 24B and the left and right ends of the stretchable portion 23B. A mechanical fastener loop 47B was sewn onto the back surface of the distal end of the stretchable waist cord 4L (3.0 cm wide), and a mechanical fastener hook 47A was sewn onto the distal end surface of the stretchable waist cord 4R (3.0 cm wide). The sternal manubrium cushioning layer 31 is made of a first layer sternal manubrium cushioning material 311 (cushioning material F5, material: polyurethane foam, apparent density 20±3 kg / m3 as specified in JIS K7222, hardness 30±10 N as specified in JIS K6400-2, specific gravity 0.02 g / cm 3 , thickness 5 mm), and a second layer of sternal manubrium cushioning material 312 (cushioning material F4, material: polyether-based polyurethane foam, apparent density 35±3 kg / m as specified in JIS K7222). 3 , hardness specified in JIS K6400-2: 125±30N, specific gravity: 0.035g / cm 3 The cushioning material used was a laminate of a first layer of cushioning material 313 (cushioning material F6, material: ethylene vinyl acetate copolymer, thickness 4 mm) and a third layer of cushioning material 314 (cushioning material F6, material: ethylene vinyl acetate copolymer, thickness 4 mm). Except for the above, the harness 103 for measuring biological signals was produced in the same manner as in Example 2. Figure 23 shows the results of the harness 103 for measuring biological signals in Example 4, which was produced in the same manner as in Example 2. １ 1.1 cm), and the elastic conductive cord 6 (electric wire S2, width 1.2 cm) are graphs showing the relationship between the elongation rate and the elongation load.

[0076] Example 5 In Example 5, the sternal manubrium support member 3A shown in Figures 8A to 8C was produced. First, a sternal manubrium connecting loop 32 was sewn to one of two hexagonally shaped sternal manubrium support members 33A (material: polyurethane). Next, the two sternal manubrium support members 33A were sandwiched and bonded to a cushioning material F6 (material: ethylene vinyl acetate copolymer resin, thickness: 4 mm, diameter: 2 cm). Furthermore, a conductive connector 53 was provided at the orthocenter of the hexagon, completing the sternal manubrium support member 3A.

[0077] (Examples 6-1 to 6-7) In Examples 6-1 to 6-7, epigastric cushioning layers and manubrium cushioning layers were manufactured using the cushioning material configuration shown in Figure 26B. The diameter of the epigastric cushioning layer was 4.5 cm, and the diameter of the manubrium cushioning layer was 3.5 cm. The cushioning material was composed of single or laminated cushioning layers from the first to fourth layers. Considering their use as epigastric cushioning layers, manubrium cushioning layers, or subclavian fossa cushioning layers, the compressive stress of the cushioning materials or cushioning layers was measured using the measurement method described below.

[0078] 12A to 12D was produced. Specifically, the extension elastic conductive cord 62 was produced using the same material as that used in Example 2, and the extension elastic conductive cord 62 was connected to the chest support member 2A and the manubrium support member 3 of Example 2, thereby obtaining the biosignal measurement harness 104.

[0079] 13A to 13D was produced. Specifically, the extension elastic conductive cord 62, the lateral chest support 12, and the subclavian fossa support 11 were produced using the same materials as those used in Example 2 above, and the other components were connected to those produced in Example 2 to obtain the biosignal measurement harness 105.

[0080] Example 9 In Example 9, the biosignal measurement harness 106 shown in Figure 14A was produced. First, a first signal transmission unit 24A was obtained using the same method as in Example 2 described above. Next, extension stretchable shoulder straps 63A (1.1 cm wide) were sewn to the left and right upper ends of the stretchable portion 23C, and loops 58 and Zeiss loops 46 were provided. The stretchable portion 23C was provided with a chest pocket 14 for accommodating a bra pad 13 and an epigastric pocket (see Figure 3C). The rest of the process was carried out using the same method as in Example 2, resulting in the biosignal measurement harness 106.

[0081] Example 10 In Example 10, chest cover 15 of the biosignal measurement harness shown in Figure 15 was produced. First, chest pocket 14 for accommodating bra pad 13 was provided in a molded stretchable section. Next, multiple snaps and Zeiss loops were sewn to the stretchable section, and multiple chest cover connecting sections 54 were provided in the stretchable section. Furthermore, extension stretchable shoulder straps 63B (1.1 cm wide) with loops 58 and Zeiss loops 46 were sewn to the left and right upper ends of the stretchable section, thereby obtaining chest cover 15. Chest cover 15 was produced by sewing multiple tapes and loops to biosignal measurement harness 101 produced in Example 2, and then connecting the chest cover 15 to the biosignal measurement harness.

[0082] (Comparative Example 1) In Comparative Example 1, commercially available biosignal monitoring wear was obtained based on the conventional technology described in the above-mentioned Patent Document 5 (WO 2021 / 177171), and the obtained biosignal monitoring wear was used as the biosignal monitoring wear of Comparative Example 1. Figure 16A is a front view of the biosignal monitoring wear of Comparative Example 1. Figure 16B is a side view of the biosignal monitoring wear shown in Figure 16A. Figure 16C is a back view of the biosignal monitoring wear shown in Figure 16A.

[0083] (Electrocardiogram Recording Using the Biological Signal Measurement Harness 100) In this evaluation, the wearer wore the biological signal measurement harness 100 of Example 1 with the stretch rate of the elastic waist cord 4 set to 145%. An electrocardiogram was recorded using electrocardiograph A (bipolar lead, 1 channel). Specifically, an electrocardiogram (CC5 lead) was recorded for 30 minutes while sleeping. The electrocardiogram is shown in FIG. 17 . ECG Viewer 2.1.7.0 (manufactured by Parama Tech) was used to display the electrocardiogram, with the bandpass filter set to OFF.

[0084] (Calculation of the Length of the Elastic Waist Cord 4 Before Wearing) The length of the elastic waist cord 4 before wearing in Example 2 was calculated as follows. The following test was conducted, and the relationship diagram shown in Figure 18 was created, with the vertical axis representing the length of the elastic waist cord before wearing and the horizontal axis representing the sum of the wearer's chest circumference and waist circumference. For example, if the sum of the wearer's chest circumference and waist circumference is 180 cm, the length of the elastic waist cord 4 before wearing can be adjusted to 48 cm on each side to adjust to a stretch load of 700 g. Test specimen preparation: First, flat elastic S3 was cut to a length of 70 cm, and an eight-hook 44 was sewn to one end, after which the front hook 43 was passed through to obtain the elastic waist cord 4. Next, a hanging wire was sewn to the end of the elastic waist cord 4 opposite the front hook 43 to obtain a 67.5 cm test specimen. Test specimen: Elastic waist cord 4 Test specimen width: 2.0 cm Test specimen length: 67.5 cm (excluding grip portion) Measuring equipment: Hand scale with a flat scale plate, 1 kg (product number: 74452, manufactured by Shinwa Measuring Instruments) Test method: First, the test specimen was hung from the measuring equipment, and the front hook 43 of the test specimen was fixed to the ground. At this time, the end on the front hook 43 side was set to 0 cm, and the height of the rubber end on the hanging wire side was set to the initial length. Next, the test specimen was stretched, and the height of the rubber end on the hanging wire side was recorded when the measuring equipment indicated loads of 300 g, 400 g, 500 g, 600 g, 700 g, 800 g, 900 g, and 1000 g. The same test was repeated while adjusting the position of the eight-ring 44 to shorten the initial length of the test specimen from 67.5 cm to 33.5 cm in 2.5 cm increments. Drawing: The vertical axis (length of the elastic waist cord before wearing) represents the initial length of each test piece, and the horizontal axis (sum of the wearer's chest circumference and waist circumference) represents the value calculated using the formula: (length of test piece at time of measurement) × 2 + (length of non-elastic portion 25) + (length supplemented by connection of front hook 43), and a relationship diagram was drawn.

[0085] (Calculation of the Length of the Elastic Shoulder Strap 5 Before Wearing) The length of the elastic shoulder strap 5 in Example 2 was calculated as follows. The following test was conducted, and the relationship diagram shown in Figure 19 was created, with the vertical axis representing the length of the elastic shoulder strap before wearing and the horizontal axis representing the wearer's shoulder length. For example, if the wearer's shoulder length is 60 cm, the length of the elastic shoulder strap 5 before wearing can be adjusted to 52 cm on each side to adjust to a stretch load of 150 g. Test specimen preparation: First, undertape (1.1 cm wide) was cut to a length of 70 cm, and an eight-ring 56 was sewn to one end, followed by a Z-ring 57 to obtain the elastic shoulder strap 5. Next, a hanging wire was sewn to the end of the elastic shoulder strap 5 opposite the Z-ring 57 to obtain a 69 cm test specimen. Test specimen: Elastic shoulder strap 5 Test specimen width: 1.1 cm Test specimen length: 60 cm (excluding grip portion) Measuring equipment: Hand scale with a flat scale plate of 0.5 kg (product number: 74451, manufactured by Shinwa Measuring Instruments) Test method: First, the test specimen was hung from the measuring equipment, and the Zet Can 57 was fixed to the ground. At this time, the rubber end on the Zet Can side was set to 0 cm, and the height of the rubber end on the hanging wire side was set to the initial length. Next, the test specimen was stretched, and the height of the rubber end on the hanging wire side was recorded when the load indicated by the measuring equipment was 50 g, 100 g, 150 g, 200 g, 250 g, or 300 g. The same test was repeated while adjusting the position of the Eight Can 56 to shorten the length of the test specimen from 60 cm to 35 cm in 2.5 cm increments. Drawing: A relationship diagram was drawn with the vertical axis (length of the elastic shoulder strap before wearing) representing the initial length of each test piece and the horizontal axis (length around the wearer's shoulders) representing the length of the test piece at the time of measurement.

[0086] (Electrocardiogram Recording Using the Biosignal Measurement Harness 101 with Changed Elongation Rate Settings) In this evaluation, the wearer wore the biosignal measurement harness 101 of Example 2 with the settings of the elongation rate of the elastic waist strap 4 and the elongation rate of the elastic shoulder straps 5 changed. Electrocardiograms were recorded at rest and while walking using electrocardiographs A (bipolar lead, two channels) and B (bipolar lead, one channel). The two electrocardiographs were connected to the biosignal measurement harness 101 via the converter 70. Measurement results for the adhesive pressure applied to the contact points of the wearer's bioelectrodes 7a to 7e were obtained by changing the elongation rate settings of the elastic waist strap 4, the elastic shoulder straps 5, and the elastic conductive straps 6 to Settings 1, 2, or 3, and wearing the biosignal measurement harness of Example 2 or the biosignal monitoring wear of Comparative Example 1. are shown in FIG. 20A . 20B shows 5-second electrocardiograms (CC5 lead, CM5 lead, NASA lead) and time-dependent changes in triaxial acceleration (solid line X indicates the vertical direction, dashed line Y indicates the horizontal direction, and dashed line Z indicates the front-to-back direction) when the biosignal measurement harness of Example 2 was worn at the same elongation rate settings 1, 2, or 3, while standing at rest and while walking. Spreadsheet software was used to plot the electrocardiograms, and no digital noise or specific frequency bands were removed using a low-pass filter that passes only low frequencies, a high-pass filter that passes only high frequencies, or a band-pass filter that combines these. In Example 2, analyzable electrocardiogram signals were obtained in all leads.

[0087] (Electrocardiogram Recording Using the Biological Signal Measurement Harness 101) In this evaluation, the wearer wore the biological signal measurement harness 101 of Example 2 with the stretch rate of the elastic waist strap 4 set to 160% and the stretch rate of the elastic shoulder straps 5 set to 131%. Electrocardiograms were recorded at rest, while running on flat ground, and during the first radio calisthenics routine using electrocardiographs A (bipolar lead, two channels) and B (bipolar lead, one channel). The two electrocardiographs were connected to the biological signal measurement harness 101 via converter 70. Figure 21A shows an electrocardiogram at rest, Figure 21B shows an electrocardiogram while running on flat ground, and Figure 21C shows a three-minute electrocardiogram during the first radio calisthenics routine, divided into minute intervals. In each figure, the first row represents an electrocardiogram measured using CC5 lead, the second row represents an electrocardiogram measured using CM5 lead, and the third row represents an electrocardiogram measured using NASA lead. 21A to 21C show the time change in three-axis acceleration (solid line X indicates the up-down direction, dashed line Y indicates the left-right direction, and dashed line Z indicates the front-to-back direction). Spreadsheet software was used to plot the electrocardiograms, and no digital noise or specific frequency bands were removed using a low-pass filter that passes only low frequencies, a high-pass filter that passes only high frequencies, or a band-pass filter that combines these. In Example 2, analyzable electrocardiogram signals were obtained in all of the CC5 lead, CM5 lead, and NASA lead.

[0088] (Calculation of the Length of the Elastic Waist Cord 4 and the Spacing of the Hook-and-Loop Fasteners) The length of the elastic waist cord 4 and the spacing of the hook-and-loop fasteners 48B in the biosignal measurement harness 102 of Example 3 were calculated as follows. The approximation formula used here is not limited to the following, as it may differ depending on the test method. For example, when five hook-and-loop fasteners 48B are arranged at 7.5 cm intervals, the sum of the chest circumference and waist circumference of the wearer can be adjusted to fit body types of 182.5 cm, 172.5 cm, 162.5 cm, 152.5 cm, and 142.5 cm. Test piece: Flat rubber S3 Test piece width: 3.0 cm Test piece length: 9 cm (excluding gripping portion) Grip length: 1 cm at top, 1 cm at bottom Measuring equipment: 2 kg flat scale (product number: 74453, manufactured by Shinwa Measuring Instruments) Test method: The test piece was stretched in 1 cm increments from 9 cm to 19 cm using a manual scale, while measuring the elongation load, and then returned to the initial length. This test was repeated three times, and the average elongation load was calculated. Next, the following approximate equation was determined, which shows the relationship between the elongation rate X of the test piece and the elongation load Y (g): Approximate formula: Y = 1426.9X - 1214.9 (R2 value = 0.9979) Elongation rate at an elongation load of 700 g: 134% Adjustment interval when elongated: 10 cm Arrangement interval of hook-and-loop 48B: 7.5 cm Formula expressing the above arrangement interval: Adjustment interval when elongated / elongation rate at an elongation load of 700 g Length of target part: 182.5 cm Formula expressing the above length: Length of target part = sum of the lengths of the wearer's chest and waist Width of non-stretchable part 25: 30 cm Width of hook-and-loop 48B: 2.5 cm Length of elastic waist cord 4L where hook-and-loop loop 48B is arranged: 56 cm Formula expressing the above length: ((length of target part - width of non-stretchable part 25 - width of hook-and-loop 48B) / elongation rate at an elongation load of 700 g) / 2 Length of elastic waist cord 4R where hook-and-loop hook 48A is arranged: 56 cm

[0089] (Calculation of the Length of Elastic Shoulder Straps 5) The length of the elastic shoulder straps 5 in the biosignal measurement harness 102 of Example 3 was calculated as follows. The approximate formula used here may vary depending on the test method, and is not limited to the following. Test piece: Flat rubber S1 Test piece width: 1.1 cm Test piece length: 12 cm (excluding gripping portion) Grip portion length: Upper end 1 cm, lower end 1 cm Measuring equipment: Hand balance with flat scale plate, 1 kg (product number: 74452, manufactured by Shinwa Measuring Instruments, Ltd.) Test method: The test piece was stretched in 1 cm increments from 12 cm to 29 cm using a hand balance, while measuring the elongation load, and then returned to the initial length. This test was repeated three times, and the average elongation load was calculated. Next, the following approximate formula was determined, which shows the relationship between the elongation rate X of the test piece and the elongation load Y (g). Approximation formula: Y = 359.95X - 299.52 (R2 value = 0.9951) Elongation rate when elongation load is 150 g: 125% Length of target part: 70 cm Formula expressing the above length: Length of target part = length around the wearer's shoulders Length of elastic shoulder strap 5: 56 cm Formula expressing the above length: Length of target part / Elongation rate when elongation load is 150 g

[0090] (Calculation of the Length of the Stretchable Conductive Cord 6) The length of the stretchable conductive cord 6 in the biosignal measurement harness 102 of Example 3 was calculated as follows. The approximate formula used here may vary depending on the test method, and is not limited to the following. Test piece: Electric wire S2 Test piece width: 1.2 cm Test piece length: 13 cm (excluding gripping portion) Grip portion length: Upper end 1 cm, lower end 1 cm Measuring equipment: Hand balance with flat scale plate 500 g (product number: 74451, manufactured by Shinwa Measuring Instruments) Test method: The test piece was stretched using a hand balance in 1 cm increments from 13 cm to 23 cm, while measuring the stretching load, and then returned to the initial length. This test was repeated three times, and the average stretching load was calculated. Next, the following approximate formula was determined, which shows the relationship between the elongation rate X of the test piece and the stretching load Y (g). Approximation formula: Y = 444.73X - 404.45 (R squared value = 0.9938) Elongation rate when elongation load is 250 g: 147% Length of target part: 18 cm Formula expressing the above length: Length of target part = length of line segment D-D' in Figure 2C Length of stretchable conductive cord 6 = length of target part / elongation rate when elongation load is 250 g: 12 cm

[0091] (Measurement of Contact Pressure of Bioelectrodes) In this measurement, an air-pack pressure sensor of a continuous contact pressure measuring device for soft surfaces (product number: AMI3037-10-II, manufactured by AMI Techno) was attached to the wearer's skin in contact with the five bioelectrodes 7 on the biosignal measurement harness 103 of Example 4. The wearer wore the biosignal measurement harness 103 of Example 4 with the elongation rate of the elastic waist strap 4 set to 136% and the elongation rate of the elastic shoulder straps 5 set to 132%. The pressure applied to the five bioelectrodes 7 was measured. The results are shown in Figure 24. In Figure 24, the vertical axis represents the contact pressure (kPa) of the bioelectrodes, and the horizontal axis represents the measurement points of each bioelectrode, corresponding to bioelectrodes 7a, 7b, 7c, 7d, and 7e shown in Figure 5B.

[0092] (Surface Temperature Measurement During Wearing Under Hot and Humid Conditions) In this measurement, the wearer wore the biosignal measurement harness 103 of Example 4, layered with a crew neck short-sleeved shirt, and maintained a seated position for 15 minutes in a test environment with a temperature of 35°C, a relative humidity of 75%, and a wind speed of 1 m / s. After the test, the skin surface temperature distribution was first photographed using a thermograph while wearing the crew neck short-sleeved shirt and the biosignal measurement harness 103 of Example 4 (see the thermograph image on the left in Figure 25). Next, the crew neck short-sleeved shirt was removed, and photographs were taken with only the biosignal measurement harness 103 of Example 4 worn (see the thermograph image in the center in Figure 25). Further photographs were taken without upper body clothing (see the thermograph image on the right in Figure 25). These photographs were taken consecutively. Figure 25 shows the measurement results on a temperature distribution scale ranging from 32.0°C to 36.0°C.

[0093] (Measurement of compressive stress of buffer material or buffer layer) In this measurement, a single-layered buffer material or a laminated buffer layer (see Fig. 26B) was molded into a circle with a diameter of 3.5 cm to serve as a test specimen. A digital scale was placed on a horizontal table. The load when the compressibility of the test specimen was 0% was set to 0 g, and the load (g) when pressure was applied to the top surface of the single-layered buffer material or the laminated buffer layer to change the compressibility was measured as the compressive stress, and the compressibility (%) and the load per unit area (g / cm 2) was determined. The relationship between the obtained compression ratio and compressive stress is shown in Figure 26A. Test specimen: Cushioning material or buffer layer in each of Example 2 and Examples 6-1 to 6-7. Test specimen diameter: 4.5 cm (Example 6-1, Example 2), 3.5 cm (Examples 6-2 to 6-7, Example 2). Test specimen thickness: Cushioning material F1 was 15.56 mm, Cushioning material F2 was 5.01 mm, Cushioning material F3 was 10.39 mm, Cushioning material F4 was 5.13 mm, Cushioning material F5 was 5.18 mm, and Cushioning material F6 was 4.30 mm. Measuring equipment: Digital scale TDS-001 PRO (manufactured by TOKAIZ), Digital scale ADKS-3000 (manufactured by Atlas). Test method: The test method will be described below as shown in (1) to (5) below, using the manubrium buffer layer of Example 2 as an example. (1) The test specimen was placed on the scale pan of a digital scale placed on a horizontal platform. The height from the horizontal platform to the top of the scale pan was 17.68 mm. The thickness of the buffer layer of Example 2 was 19.82 mm, the sum of the thicknesses of buffer materials F4, F3, and F6. The height from the horizontal platform to the top of the buffer layer of Example 2 was 37.50 mm. (2) Next, four 7.81 mm thick plates and one 4.37 mm thick plate were stacked on the horizontal platform to form support platforms, and two support platforms were installed on both sides (left and right) of the digital scale. The height from the horizontal platform to the top of the support platforms was 35.61 mm. (3) Five sheets of 0.254 mm thick paper were then placed between the scale pan and the test specimen to adjust the height from the horizontal platform to 38.77 mm, which was set as the zero point, representing the load at 0% compression. At this time, the difference between the top surface of the buffer layer of Example 2 and the top surfaces of the left and right support bases was 38.77 mm - 35.61 mm = 3.16 mm. (4) Then, a 50 mm wide plate was placed on the top surface of the buffer material of Example 2 and the top surfaces of the left and right support bases, and a load of approximately 650 g was applied to compress the buffer material, which was then held for 30 seconds. At this time, the digital scale indicated a load of 56 g. The compression rate was calculated to be 3.16 mm / 19.82 mm = 0.159 (15.9%), and the load per unit area was 56 g / ((3.5 / 2) 2 ×3.14)=5.82g / cm 2(5) The height of the upper surface of the buffer layer was adjusted with 0.254 mm thick paper, and the height of the upper surface of the support base was adjusted with a combination of a 7.81 mm thick plate and a 4.37 mm thick plate, thereby changing the difference between the upper surface of the buffer material and the upper surface of the support base, and the load during compression, compression rate, and load per unit area were calculated.

[0094] (Electrocardiogram Recording Using the Biological Signal Measurement Harness 104) In this evaluation, the wearer wore the biological signal measurement harness 104 of Example 7. Electrocardiograms were recorded while standing at rest and while walking using electrocardiographs A (bipolar lead, two channels) and B (bipolar lead, one channel). The two electrocardiographs were connected to the biological signal measurement harness 104 via the converter 70. The obtained five-second electrocardiogram and the time change in three-axis acceleration (solid line X indicates the up-down direction, dashed line Y indicates the left-right direction, and dashed line Z indicates the front-back direction) are shown in FIG. 27. The five-second electrocardiogram of Example 7 was recorded, from the top, using the V5 positive electrode and the negative electrode at the left subclavian fossa, the V5 positive electrode and the V 5R These electrocardiograms were obtained from CC5 lead using a negative electrode at the sternal xiphoid process and a negative electrode at the left subclavian fossa, and from CC6 lead using a positive electrode at the sternal xiphoid process and a negative electrode at the left subclavian fossa. Spreadsheet software was used to plot these electrocardiograms, and no digital noise or specific frequency bands were removed using a low-pass filter that passes only low frequencies, a high-pass filter that passes only high frequencies, or a band-pass filter that combines these. In Example 7, analyzable electrocardiogram signals were obtained from all leads.

[0095] (Electrocardiogram Recording Using the Biological Signal Measurement Harness 105) In this evaluation, the wearer wore the biological signal measurement harness 105 of Example 8. Electrocardiograms were recorded while standing at rest and while walking using electrocardiographs A (bipolar lead, two channels) and B (bipolar lead, one channel). The two electrocardiographs were connected to the biological signal measurement harness 104 via the converter 70. The obtained 5-second electrocardiogram and the time change in three-axis acceleration (solid line X indicates the up-down direction, dashed line Y indicates the left-right direction, and dashed line Z indicates the front-to-back direction) are shown in FIG. 27 . The 5-second electrocardiograms of Example 8 were obtained, from top to bottom, using the lead formed by the negative electrode V5 and the positive electrode V8, the lead formed by the negative electrode at the left subclavian fossa and the positive electrode V8, and the lead formed by the negative electrode at the left subclavian fossa and the positive electrode V6. These electrocardiograms were plotted using spreadsheet software, and no digital noise or specific frequency bands were removed using a low-pass filter that passes only low frequencies, a high-pass filter that passes only high frequencies, or a band-pass filter that combines these. In Example 8, analyzable electrocardiogram signals were obtained for all leads.

[0096] (Long-Term Electrocardiogram Recording During Daily Life) In this evaluation, the wearer wore the biosignal measurement harness 101 of Example 2. Three electrocardiographs B (bipolar lead, one channel) were used to record electrocardiograms during daily life. The three electrocardiographs B were connected to the biosignal measurement harness 101 via converters (not shown) different from the converter 70, and recordings were performed using AS lead (CM5 lead), ES lead (NASA lead), and IS lead (CM5R lead). AS lead, ES lead, and IS lead refer to leads used to record electrocardiograms, respectively, with the A electrode located in the fifth intercostal space on the left mid-axillary line, the E electrode located below the sternum at the same height as the fifth intercostal space, and the I electrode located in the fifth intercostal space on the right mid-axillary line as the positive electrode, and the S electrode located above the sternum as the common negative electrode. In this case, the QRS waves of the electrocardiogram waveform typically decrease in magnitude in the order of AS, ES, and IS. The hourly electrocardiogram acquisition rate was calculated by evaluating the electrocardiograms obtained from these leads using the same analysis algorithm and using the formula: (recording time - non-analysis time) / recording time. The activity score acc was calculated based on the triaxial acceleration values, with values ​​of 0 at rest, approximately 5 during walking, and approximately 10 during step-up and step-down. As shown in Figures 21D and 21E, high electrocardiogram acquisition rates were obtained with the three leads in both Period 1, which was recorded over seven non-consecutive days, and Period 2, which was recorded over seven consecutive days, demonstrating that long-term recording in daily life was possible.

[0097] When any of the biosignal measurement harnesses of Examples 3, 4, 6-5 to 6-7, 9, and 10 is worn, an electrocardiogram can be measured in the same manner as in Example 1 (see FIG. 17), Example 2 (see FIGS. 20B, 21A, 21B, 21C, 21D, and 21E), Example 7 (see FIG. 27), and Example 8 (see FIG. 27). An electrocardiogram can also be measured using the manubrium support 3 of Example 5, but the CM5 lead and NASA lead are susceptible to the influence of body movement noise.

[0098] (Measurement of dressing time and undressing time) In this measurement, the wearer wore the biosignal measurement garment 101 of Example 2, and the dressing time and undressing time were measured three times each, and the average time (seconds) was calculated. Next, the wearer wore the biosignal monitoring garment of Comparative Example 1, and the dressing time and undressing time were measured three times each, and the average time (seconds) was calculated. These measurement results are shown in Figure 22. As shown in Figure 22, the dressing and undressing time of Example 2 was shorter than that of Comparative Example 1.

[0099] (Calculation of Coverage Area) To calculate the coverage area, the following photographs were printed on cardboard, and the weight of the resulting cardboard was measured after cutting out the relevant portions. (1) Front of the torso's trunk (2) Back of the torso's trunk (3) Front of the biosignal measurement harness 101 of Example 2 worn on the torso (4) Back of the biosignal measurement harness 101 of Example 2 worn on the torso. Based on the weight ratio of the front of the biosignal measurement harness 101 (0.51 g) to the front of the torso's trunk (2.25 g), the area ratio of the front of the biosignal measurement harness 101 to the front of the torso's trunk was calculated to be 23%. Furthermore, based on the weight ratio of the back of the biosignal measurement harness 101 (0.20 g) to the back of the torso's trunk (2.37 g), the area ratio of the back of the biosignal measurement harness 101 to the back of the torso's trunk was calculated to be 12%.

[0100] The biosignal measurement harness of the present invention has been described above using the examples of Embodiments 1 to 6, but the present invention is not limited to Embodiments 1 to 6, and configurations in which the above-mentioned components are appropriately combined are also included in the present invention. In addition, other invention embodiments, examples, operational techniques, etc. made by those skilled in the art based on the above-mentioned Embodiments 1 to 6 are all included in the scope of the present invention.

[0101] As described above, the biosignal measurement harness according to the present invention is useful for single-lead and multi-lead electrocardiogram measurement of a wearer, and is particularly suitable for long-term comfortable wear in daily life. Furthermore, it can be used not only for medical purposes but also for non-medical purposes.

[0102] DESCRIPTION OF SYMBOLS 100, 101, 102, 103, 104, 105, 106...Biological signal measurement harness 2, 2A, 2B, 2C...Chest support 3, 3A...Sternal manubrium support 4, 4L, 4R...Elastic waist strap 5, 5L, 5R...Elastic shoulder strap 6...Elastic conductive strap 7, 7a, 7b, 7c, 7d, 7e...Bioelectrode 8...Conductive fiber 10...Seam tape 11...Subclavian fossa support 12...Lateral chest support 13...Bra pad 14...Chest pocket 15...Chest cover 21...Epigastric cushioning layer 22, 22A...Epigastric pocket 23, 23A, 23B, 23C...Elastic section 24, 24A, 24B...First signal transmission section 25...Non-elastic section 26...Auxiliary elastic member 27...Step cushioning material 31...Sternal manubrium cushioning layer 32...Sternal manubrium connecting loop 33, 33A...Sternal manubrium support member 34...Second signal transmission unit 43...Front hook 44...Eight-ring 46...Z-ring 47A...Mechanical fastener hook 47B...Mechanical fastener loop 48A...Hook-and-loop fastener hook 48B...Hook-and-loop fastener loop 51...Measuring instrument connector 52, 52a, 52b, 52c, 52d, 52e...Electrode connector 53...Conductive connector 54...Chest cover connecting unit 56...Eight-ring 57...Z-ring 58...Loop 61...Electrical wire 62...Extendable conductive cord 63A, 63B...Extendable shoulder cords 211...First layer epigastric cushioning material 212...Second layer epigastric cushioning material 213...Mechanical fastener hook 214... Mechanical fastener loop 311... First layer of sternal manubrium cushioning material 312... Second layer of sternal manubrium cushioning material 313... Third layer of sternal manubrium cushioning material 70... Transducer 71... Transducer base 72... Anti-slip material 90, 91... Electrocardiograph K1, K2... Area

Claims

1. A biosignal measurement harness comprising: a chest support having a plurality of bioelectrodes, a measuring instrument connector for connecting a biosignal receiving device, a first signal transmission unit for connecting the plurality of bioelectrodes to the measuring instrument connector, a non-stretchable unit for supporting the plurality of bioelectrodes, the measuring instrument connector and the first signal transmission unit, and a stretchable unit superimposed on the non-stretchable unit; and a pair of left and right stretchable cords connected to the left and right ends of the non-stretchable unit and the stretchable unit that constitute the chest support, respectively, wherein the pair of left and right stretchable cords each have a length adjustment mechanism and a connecting mechanism, and secure the plurality of bioelectrodes to the human body.

2. The biosignal measurement harness according to claim 1, wherein the pair of left and right elastic cords are a pair of left and right elastic waist cords, which, when worn, pass over the sides of the body, cross or connect in a sliding manner at the lower back, and then pass further over the sides of the body and connect in the front navel or front lower abdominal area, thereby fixing the multiple bioelectrodes to the human chest.

3. A biosignal measurement harness as claimed in claim 1 or 2, comprising: a sternal manubrium support having one bioelectrode and a second signal transmission unit connecting the one bioelectrode and an electrode connector; an elastic conductive string connecting the chest support and the sternal manubrium support; and a pair of elastic shoulder straps, one end of which is connected to the sternal manubrium support and the other end of which is connected to the left and right ends of the elastic unit, respectively, wherein the elastic conductive string extends over the sternum and connects the first signal transmission unit and the second signal transmission unit, and the pair of elastic shoulder straps each have a length adjustment mechanism and a connecting mechanism, and when worn, they pass from the sternal manubrium through the shoulders and down the sides of the body and connect to the left and right ends of the elastic unit, respectively, thereby fixing the one bioelectrode to the human sternal manubrium.

4. A biosignal measurement harness as claimed in claim 1 or 2, comprising: a subclavian fossa support having one bioelectrode and a second signal transmission unit connecting the one bioelectrode and an electrode connector; an elastic conductive string connecting the chest support and the inclavian fossa support; and a pair of left and right elastic shoulder straps, one end of which is connected to the inclavian fossa support and the other end of which is connected to the left and right ends of the elastic unit, respectively, wherein the elastic conductive string connects the first signal transmission unit and the second signal transmission unit, and the pair of left and right elastic shoulder straps each have a length adjustment mechanism and a connection mechanism, and when worn, one of the shoulder straps passes from the shoulder on the inclavian fossa support side over the side of the body and connects to the end of the elastic unit, and the other passes from the shoulder on the inclavian fossa support side diagonally across the back and connects to the other end of the elastic unit, thereby fixing the one bioelectrode to the inclavian fossa.

5. A lateral chest support comprising: first, a plurality of bioelectrodes to be placed on the lateral chest, a measuring instrument connector for connecting a biosignal receiving device, a first signal transmission section connecting the plurality of bioelectrodes to the measuring instrument connector, a non-stretchable section supporting the plurality of bioelectrodes, the measuring instrument connector, and the first signal transmission section, and a stretchable section overlapping the non-stretchable section; second, a pair of left and right stretchable waist cords respectively connected to the left and right ends of the non-stretchable section and the stretchable section constituting the lateral chest support; third, a subclavian fossa support having one bioelectrode and a second signal transmission section connecting the one bioelectrode to the electrode connector; fourth, a stretchable conductive cord connecting the lateral chest support and the subclavian fossa support; and fifth, a pair of left and right stretchable shoulder straps one end of which is connected to the subclavian fossa support and the other end of which is connected to the left and right ends of the stretchable section of the lateral chest support, Sixth, the pair of elastic waist cords on the left and right each have a length adjustment mechanism and a connecting mechanism, and when worn, one passes along the side of the body, diagonally across the lower back, and then passes along the side of the body to the navel or lower abdomen on the front, and the other extends from the back, along the side of the body, and to the navel or lower abdomen on the front and connects, thereby fixing the multiple bioelectrodes to the human chest; Seventh, the pair of elastic shoulder straps on the left and right each have a length adjustment mechanism and a connecting mechanism, and when worn, one passes along the side of the body, across the front, and connects to the end of the elastic part, and the other passes along the shoulder of the infraclavicular fossa, diagonally across the back, and connects to the other end of the elastic part, thereby fixing one bioelectrode to the infraclavicular fossa.

6. The harness for measuring biosignals according to claim 3, wherein the chest support covers the upper part of the human chest, or covers the upper part of the human chest in combination with a detachable chest covering.

7. The biosignal measurement harness according to claim 3, wherein the covering area is 30% or less of the front of the wearer's trunk and 20% or less of the back of the wearer's trunk.

8. The biosignal measurement harness according to claim 3, wherein a buffer layer made of buffer materials with different compressive stresses is provided on the back surface of at least one of the bioelectrodes.

9. The biosignal measurement harness according to claim 8, wherein the compressive stress on the bioelectrode side of the buffer material constituting the buffer layer is smaller than the compressive stress on the opposite side to the bioelectrode side.

10. The biosignal measurement harness according to claim 3, wherein the bioelectrodes are arranged in accordance with any one of the following: (a) CC5 lead; (b) CM5 lead; (c) NASA lead; (d) CC5 lead and CM5 lead; (e) CC5 lead and NASA lead; (f) CM5 lead and NASA lead; (g) CC5 lead, CM5 lead and NASA lead; (h) EASI lead.

11. The biosignal measurement harness according to claim 3, which uses a transducer for connecting at least one of the biosignal receiving devices.

Images