KR101840115B1 - garment for measuring vital signals using conductive member placed on skin - Google Patents

Abstract

A biological signal measurement appara- tus using a conductive member disposed on the skin is disclosed. The bio-signal measurement clothes are disposed in a conductive member disposed on a skin of an object and a non-conductive garment worn by the object, and are continuously or intermittently in electrical contact with the conductive member in accordance with the movement of the object, And a bio-signal sensing electrode. The bio-signal sensing electrode is connected to the bio-signal measuring device to provide the bio-signal to the bio-signal measuring device. The bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal received from the bio-signal sensing electrode. The conductive member is obtained by coating the skin with a conductive material having fluidity and then drying the conductive material. The conductive material may be brought into close contact with the surface of the skin by the fluidity in the process of coating the skin, thereby reducing the contact resistance between the bio-signal sensing electrode and the skin.

Description

[0001] The present invention relates to a biological signal measuring apparatus using a conductive member disposed on a skin,

TECHNICAL FIELD [0002] The present invention relates to a bio-signal measurement apparel, and more particularly to a bio-signal measurement appara- tus, and more particularly to a bio-signal measuring appa- ratus, which comprises a conductive member disposed on a skin through coating a conductive substance having fluidity on the skin, The present invention relates to a bio-signal measurement appara- tus capable of measuring a bio-signal through a method of mutually contacting a signal-detecting electrode or a pulse measuring unit. The conductive member is obtained by coating the conductive material having fluidity on the skin and drying the conductive member, so that the contact resistance between the conductive member and the skin can be reduced.

This study was conducted as a result of the research of the basic research project of the research field of the Korea Research Foundation (assignment number NRF-2013R1A2A2A03016489).

In recent years, there has been a growing need for systematic management of personal health from a social point of view, due to increased interest in health and changes in lifestyle and entry into an aging society. As a result, there is a growing demand for technologies that can systematically monitor and manage the health of individuals.

Particularly, since the bio-signal measuring clothes are in contact with the human body anytime and anywhere, they are suitable for measuring bio-signals, and studies and attempts have been made to easily mount various kinds of bio-signal measuring sensors in bio-signal measuring clothes .

Also, through the smart clothing worn on the human body, elderly people, health impaired people, and outpatients can check their daily health without visiting the hospital. Individual health information identified through smart clothing can be provided to hospitals in wired and wireless. Smart apparel is expected to contribute to medical welfare by collecting health information of individuals in medical blind spot or needing treatment and providing them to hospitals.

Conventional technologies related to the measurement of biological signals include Korean Patent No. KR 10-1384755 entitled " Sports Bra for Electrocardiogram Measurement Using a Dry Electrode ", Korean Patent Publication No. KR 10-2013-0164479 " Smart Wear System Using Wearable Device " have. These conventional techniques have a common point with the present invention in that they take a method of measuring a living body signal through a method in which the skin contacts with a living body signal sensing electrode attached to clothes. However, these prior arts have difficulty in accurately measuring the biological signals due to the large contact resistance between the skin and the electrode pad for measurement of the biological signals, and the motion noise due to the movement of the wearer during the process of directly contacting the bio- There was a problem.

In order to solve such problems, conventionally, water or electrolytic gel is applied to the skin before measurement of a living body signal, and a living body signal is measured through a living body signal sensing electrode. However, there was a problem that when the water or electrolytic gel dried, the bio-signal was not measured or the measurement quality deteriorated. In addition, when an electrolytic gel is used, noise due to the clearance between the bio-signal sensing electrode and the skin due to movement of the subject is caused, and there is a problem of cosmetic appearance due to wiring.

In order to solve the problems of the conventional art described above, a technique disclosed in the present application has been developed to solve the above-described problems of the prior art. In constructing a bio-signal measurement appara- tus, a conductive member is applied to the skin to closely contact the bio- And a skin contact resistance between the skin and the skin can be reduced.

In one embodiment, a bio-signal measurement apparel using a conductive member disposed on the skin is disclosed. The bio-signal measurement clothes are disposed in a conductive member disposed on a skin of an object and a non-conductive garment worn by the object, and are continuously or intermittently in electrical contact with the conductive member in accordance with the movement of the object, And a bio-signal sensing electrode. The bio-signal sensing electrode is connected to the bio-signal measuring device to provide the bio-signal to the bio-signal measuring device. The bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal received from the bio-signal sensing electrode. The conductive member is obtained by coating the skin with a conductive material having fluidity and then drying the conductive material. The conductive material may be brought into close contact with the surface of the skin by the fluidity in the process of coating the skin, thereby reducing the contact resistance between the bio-signal sensing electrode and the skin.

The bio-signal measurement appara- tus may further comprise a pulse measurement unit disposed in the non-conductive apparel. The pulse measuring part may be disposed in the nonconductive garment so as to face the arterial blood vessel. Wherein the pulse measuring unit analyzes at least any one of a change in external shape of the arterial blood vessel caused by contraction and relaxation of the heart of the subject, a pressure change, a change in light absorption amount, Can be detected. The pulsation signal of the object sensed by the pulse measurement unit may be provided to the health information analysis unit, and the health information analysis unit may analyze the health information of the object from the biological signal and the pulse signal.

In another embodiment, a bio-signal measurement apparel using a conductive member disposed on the skin is disclosed. The bio-signal measurement garment includes a conductive member, a non-conductive garment, a bio-signal sensing electrode, and a pulse measurement unit. The conductive member is disposed on the skin of the object. The nonconductive garment is extended to face the at least one of the wrist, ankle, neck and a combination of the above-referred to as a pulse measuring point, of the object to be worn by the object. The bio-signal sensing electrode is disposed in the non-conductive clothing, and can continuously or intermittently contact the conductive member in accordance with the movement of the object to sense a bio-signal. Wherein the pulsation measuring unit is disposed in the nonconductive garment so as to face the arterial blood vessel at the pulse measuring point, wherein the pulsation measuring unit changes the shape of the arterial blood vessel, changes in pressure, And a pulse signal of the object is detected by analyzing at least one of the change, the change of the electrical characteristic, and the combination thereof. In this case, the bio-signal detecting electrode and the pulse measuring unit may be connected to the bio-signal measuring device to provide the bio-signal and the pulse signal to the bio-signal measuring device, respectively. The bio-signal measurement apparatus includes a health information analysis unit for analyzing health information of the object from the bio-signal and the pulse signal. The conductive member is obtained by coating the skin with a conductive material having fluidity and then drying the conductive material. The conductive material is brought into close contact with the surface of the skin due to the fluidity in the process of coating the skin, thereby reducing contact resistance between the bio-signal sensing electrode and the skin.

The health information analyzing unit may generate the electrocardiogram waveform of the object from the bio-signal, and may generate the pulse waveform of the object from the pulse signal. The health information analysis unit may detect one or more minutiae points of the pulse wave pattern. In this case, the health information analyzing unit detects a time when a peak value of the ventricular depolarization timing occurs from the generated electrocardiographic waveform - hereinafter referred to as T_Rp, and a time at which the feature point detected from the pulse waveform is less than T_Hp The pulse wave transmission time is extracted from the T_Hp and the T_Rp, and the blood pressure of the object is calculated from the extracted pulse wave transmission time.

The blood pressure of the subject may include systolic blood pressure and diastolic blood pressure. Wherein the systolic blood pressure is calculated by applying the pulse wave propagation time to a first regression equation, and the diastolic blood pressure is calculated by multiplying the pulse wave propagation time, the body characteristic information of the object, the electrocardiographic waveform, 2 regression equation.

The bio-signal sensing electrode may be disposed in the non-conductive garment in a manner that woven conductive fibers into the non-conductive garment. The bio-signal measuring apparatus may be mounted on the pulse measuring unit. The pulse measuring unit may be detachably attached to the nonconductive garment. In this case, the non-conductive garment includes a lead extending to a corresponding point of the non-conductive garment, one end of which is electrically connected to the bio-signal sensing electrode and the other end of which is detachably attached to the non-conductive garment . At this time, the conductor may be formed by weaving conductive fibers in the non-conductive clothing. The living body signal measuring device may be provided with the living body signal and the pulse signal from the living body signal detecting electrode and the pulse measuring unit by being brought into contact with the other end of the lead in the process of attaching the pulse measuring unit to the detachable attachment point have.

The non-conductive clothing may include a first through-hole formed adjacent to the bio-signal sensing electrode. The conductive member may be formed by coating the conductive material on the skin through the first through hole and drying the conductive material, so that the bio-signal sensing electrode and the conductive member can be opposed to each other.

Meanwhile, the bio-signal sensing electrode may include a second through hole formed through the inside thereof. The skin on which the conductive member is disposed can communicate with the outside through the second through hole. The conductive member may be formed by coating the conductive material on the skin through the second through hole and drying the conductive material, so that the bio-signal sensing electrode and the conductive member can be opposed to each other.

In addition, the bio-signal measurement appara- tus may further include a conductive material supply unit for accommodating the conductive material. The conductive material supply part may include a container, a diffusion plate, and a connection part. The container may contain the conductive material therein and may have an opening through which the conductive material may be discharged by an applied external force. The diffusion plate may be disposed opposite to the opening. The connection portion may connect the container and the diffusion plate. The conductive material may be discharged through the opening by inserting the opening into the second through hole and applying the external force to the container. In this case, the conductive material is diffused by the diffusion plate in the discharging process, is provided to the skin and dried, so that the conductive member can be arranged to face the bio-signal sensing electrode in a self-aligning manner .

The bio-signal measurement garment disclosed in this specification measures a bio-signal through a method of contacting a bio-signal sensing electrode disposed on a non-conductive garment with a conductive member disposed on a skin of an object. The conductive member is obtained by applying a conductive substance having fluidity to the skin and drying the contact member, so that the contact resistance between the conductive member and the skin can be reduced. The bio-signal sensing electrode is in electrical contact with the skin of the object via the conductive member without directly contacting the skin of the object. The contact resistance between the bio-signal sensing electrode and the skin of the object is lowered, so that the bio-signal measurement clothing disclosed in this specification provides a technique capable of stably detecting a bio-signal even when the object is resting or moving .

In addition, the bio-signal measurement appara- tus disclosed in this specification includes a pulse measurement unit, and a pulse signal of an object sensed by the pulse measurement unit is provided to the bio-signal measurement apparatus. The bio-signal measuring apparatus can calculate the blood pressure of the object from the pulse signal provided from the pulse measuring unit and the electrocardiogram signal provided from the bio-signal sensing electrode, and can inform the object of the blood pressure. Accordingly, the bio-signal measuring clothes disclosed in this specification can provide an effect that an object (for example, a wearer) can self-measure his / her blood pressure.

The foregoing provides only a selective concept in a simplified form as to what is described in more detail hereinafter. The present disclosure is not intended to limit the scope of the claims or limit the scope of essential features or essential features of the claims.

BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 illustrates a bio-signal measurement apparel disclosed herein in accordance with one embodiment.
2 is a view showing a pulse measuring unit disclosed in this specification according to an embodiment.
3 is a view for explaining a method of disposing a conductive material on the skin through the conductive material supply unit disclosed in this specification according to an embodiment.
4 is a graph showing electrocardiographic waveforms measured by a bio-signal measuring apparata disclosed in this specification according to an embodiment.
FIG. 5 is a diagram for explaining a method of obtaining feature points from a pulse waveform measured by a bio-signal measurement appara- tus disclosed in this specification according to an embodiment.
FIG. 6 is a diagram for explaining a method of determining a pulse wave transmission time from an ECG waveform and a pulse waveform measured by a bio-signal measurement appara- tus disclosed in this specification according to an embodiment.
7 is a view showing a bio-signal measurement apparel disclosed in this specification according to another embodiment.

Hereinafter, embodiments disclosed in this specification will be described in detail with reference to the drawings. Like reference numerals in the drawings denote like elements, unless the context clearly indicates otherwise. The exemplary embodiments described above in the detailed description, the drawings, and the claims are not intended to be limiting, and other embodiments may be utilized, and other variations are possible without departing from the spirit or scope of the disclosed technology. Those skilled in the art will appreciate that the components of the present disclosure, that is, the components generally described herein and illustrated in the figures, may be arranged, arranged, combined, or arranged in a variety of different configurations, all of which are expressly contemplated, As shown in FIG. In the drawings, the width, length, thickness or shape of an element, etc. may be exaggerated in order to clearly illustrate the various layers (or films), regions and shapes.

When a component is referred to as being "positioned" to another component, it may include a case where the component is directly disposed on the other component as well as a case where an additional component is interposed therebetween.

When one component is referred to as being "connected" to another component, it may include a case where the one component is directly connected to the other component as well as a case where additional components are interposed therebetween.

When one component is referred to as being "mounted" to another component, it may include the case where the component is directly mounted on the other component as well as the case where additional components are interposed therebetween.

The description of the disclosed technique is merely an example for structural or functional explanation and the scope of the disclosed technology should not be construed as being limited by the embodiments described in the text. That is, the embodiments are to be construed as being variously embodied and having various forms, so that the scope of the rights of the disclosed technology should be understood to include equivalents capable of realizing the technical ideas.

It is to be understood that the singular " include " or " have " are to be construed as including the stated feature, number, step, operation, It is to be understood that the combination is intended to specify that it is present and not to preclude the presence or addition of one or more other features, numbers, steps, operations, components, parts or combinations thereof.

All terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the disclosed technology belongs, unless otherwise defined. Terms defined in commonly used dictionaries should be interpreted to be consistent with meaning in the context of the relevant art and can not be construed as having ideal or overly formal meaning unless expressly defined in the present application.

The term " object " used in the present specification should be understood as an expression that encompasses an animal or the like capable of detecting a biological signal in addition to a person.

BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 is a diagram illustrating a bio-signal measurement apparel disclosed herein in accordance with one embodiment. FIG. 1 (a) is a conceptual diagram of a bio-signal measurement appara- tus, and FIG. 1 (b) is a view showing a cross-sectional view along AA 'line of a bio-

2 is a view showing a pulse measuring unit disclosed in this specification according to an embodiment.

3 is a view for explaining a method of disposing a conductive material on the skin through the conductive material supply unit disclosed in this specification according to an embodiment.

4 is a graph showing electrocardiographic waveforms measured by a bio-signal measuring apparata disclosed in this specification according to an embodiment.

FIG. 5 is a diagram for explaining a method of obtaining feature points from a pulse waveform measured by a bio-signal measurement appara- tus disclosed in this specification according to an embodiment. FIG. 5A is a diagram showing the maximum point of the pulse waveform, FIG. 5B is a diagram showing the lowest point of the pulse waveform, FIG. 5C is a diagram showing the average point of the pulse waveform, (F) is a view showing an intersection point of one tangent line of the pulse waveform, (g) is a view showing the maximum point of the differential pulse, (e) is a diagram showing the second order differential maximum point of the pulse waveform, (H) is a diagram showing distribution of minutiae points that can be detected in the pulse waveform. Fig.

FIG. 6 is a diagram for explaining a method of determining a pulse wave transmission time from an ECG waveform and a pulse waveform measured by a bio-signal measurement appara- tus disclosed in this specification according to an embodiment.

The bio-signal measurement apparel 100 includes a conductive member 110, a non-conductive apparel 120, a bio-signal sensing electrode 130, and a bio-signal measurement device 140. In some other embodiments, the bio-signal measurement apparel 100 may optionally further include a pulse measurement unit 150. [ In some other embodiments, the bio-signal measurement apparel 100 may optionally further include a conductive material supplier 160.

The conductive member 110 is disposed on the skin 10 of the object (not shown). The conductive member 110 is obtained by coating the skin 10 with the conductive material 110a having fluidity and then drying the conductive material 110a. The conductive material 110a is brought into close contact with the surface of the skin 10 due to the fluidity in the process of coating the skin 10 to form the conductive member 110 and the skin 10, The bio-signal sensing electrode 130 can sense a bio-signal in a low contact resistance environment.

Various materials can be used as the conductive material 110a. As the conductive material 110a, various types of conductive material 110a such as an ink type, a paste type, and the like may be used. More specifically, the conductive material 110a may be an ink type ink having a low viscosity (less than about 10 Kcps), an adhesive type having a medium viscosity (about 10 to about 150 Kcps), or an adhesive type having a high viscosity To about 700 Kcps) may be used. Here, the conductive material 110a may be a method of using the hand, using a tube containing the conductive material 110a, or providing the conductive material 110a to the skin 10 by using a pen containing the conductive material 110a As shown in FIG.

For example, the conductive material 110a may be composed of polyvinyl alcohol, butylene glycol, polyquat, ethanol, carbon powder, and water. The polyvinyl alcohol is used for easily peeling off the conductive member 110 obtained by drying the conductive material 110a. Butylene glycol is used as a moisturizer. The polyquat is used to increase the viscosity of the conductive material 110a. Ethanol is used to rapidly dry and harden the conductive material 110a that is applied to the skin 10. The carbon powder is used for imparting conductivity to the conductive material 110a. The carbon powder may be, for example, graphite powder. At this time, although the carbon powder is not toxic to the human body, there is a concern that when the carbon powder penetrates the skin 10 of the object, the skin 10 may cause troubles and other diseases. Therefore, it may be desirable to use graphite powder having a size of about 74 to about 90 μm, which is larger than a human average pore size of about 50 μm, as a carbon powder. As an example for the understanding, the conductive material 110a containing various components in addition to the example described above may be used as the conductive material 110a.

The nonconductive garment 120 is worn by the object. The non-conductive clothing 120 may include a first through hole 122 formed adjacent to the bio-signal sensing electrode 130. The conductive member 110 may be obtained by coating the skin 10 with the conductive material 110a through the first through hole 122 and then drying the conductive material 110a. At this time, the conductive material 110a may be coated on the skin 10 through the first through hole 122 and then dried, so that the conductive member 110 may face the bio-signal sensing electrode 130. [ The nonconductive clothes 120 are electrically connected at one end to the bio-signal sensing electrode 130 and at the other end of the non-conductive apparel 120 where the pulse measuring unit 150 is detachably attached Quot;). ≪ / RTI >

Conductive wire 124 may be formed by weaving conductive fibers on nonconductive apparel 120. In one example, the conductor 124 may have elasticity and may be manufactured through substantially the same process as the method of manufacturing a fabric having span characteristics. Conductive wire 124 may be formed, for example, by applying a conductive material to a nonconductive apparel 120 in the form of a thin film, or by weaving a composite compound, such as a conductive polymer, .

The bio-signal sensing electrode 130 is disposed on the non-conductive clothing 120 and continuously or intermittently contacts the conductive member 110 in accordance with the movement of the object to sense the bio-signal. The bio-signal sensing electrode 130 is connected to the bio-signal measuring device 140 to provide the bio-signal to the bio-signal measuring device 140.

In one example, the bio-signal sensing electrode 130 may be disposed in the non-conductive apparel 120 in a manner that woven conductive fibers into the non-conductive apparel 120. The bio-signal sensing electrode 130 may be disposed on the nonconductive apparel 120 by way of, for example, weaving the nonconductive apparel 120 utilizing non-conductive fibers and conductive fibers. Alternatively, the bio-signal sensing electrode 130 may be woven in the form of a fiber pad into conductive fibers and then disposed in the non-conductive clothing 120 in a detachable manner.

The living body signal such as electrocardiogram, electromyogram and the like can be measured through the living body signal sensing electrode 130.

The electrocardiogram (ECG) is an electrical activity generated by depolarization and repolarization of the atria and ventricles. The bio-signal sensing electrode 130 may measure the electrocardiogram by sensing a potential difference generated by the depolarization of the atrium and the ventricle and the repolarization.

The electrocardiogram waveform 134 is composed of a P wave 134a, a Q wave 134b, an R wave 134c, an S wave 134d and a T wave 134e, as shown in Fig.

The P wave 134a is a wavelength that occurs during the diastole of the ventricle while depolarizing the atrium through a stimulus delivered to the atrium through an SA node (sinoatrial node) located in the right atrium wall. The depolarization of the atrium is initiated in the vicinity of the effervescence and proceeds from the right atrium to the left atrium myocardium. The first part of the P wave 134a represents the depolarization of the right atrium and the rear part of the P wave 134a represents the depolarization of the left atrium. The P wave 134a is upward and slightly rounded.

The Q wave 134b, the R wave 134c and the S wave 134d are wavelengths appearing at the depolarization timing of the ventricle. The depolarization of the ventricles begins at the left side of the ventricular septum near the atrioventricular junction and proceeds to the right side of the interventricular septum across the interventricular septum. The Q wave 134b represents the depolarization of the ventricular septum and is defined as a downward wave recorded in front of the R wave 134c. The R wave 134c and the S wave 134d represent the depolarization of the ventricle in the left and right ventricles simultaneously. The R wave 134c is defined as the first recorded upward wave and the S wave 134d is defined as the downward wave recorded after the R wave 134c.

T wave 134e is a wavelength appearing at the repolarization time of the ventricle. The repolarization proceeds more slowly than the depolarization. Therefore, the T wave 134e is an upward wave, which is longer than the Q wave 134b, the R wave 134c and the S wave 134d, and the amplitude is also lower.

The electromyogram (EMG) is an electrical activity generated by muscle contraction. The bio-signal sensing electrode 130 may be disposed at a portion composed of full-thickness cells, nerve fibers, nerve-muscle joints, and muscle fibers. In this case, the bio-signal sensing electrode 130 may measure the electromyogram by sensing a potential difference generated during the contraction of the muscle.

In FIG. 1, a biological signal measurement apparel 120 in which two bio-signal sensing electrodes 130 are disposed is shown as an example. In FIG. 1, two conductive lines 124, each having one end connected to two bio-signal sensing electrodes 130, are illustrated as an example. In this case, the other ends of the two conductors 124 may be connected to each other with a detachable attachment point 126 disposed on the arm portion of the non-conductive garment 120, respectively. The bio-signal sensed by the bio-signal sensing electrode 130 may be provided to the attachment / detachment point 126 via the wire 124. In this case, the bio-signal measuring device 140 may be electrically connected to the detachable attachment point 126 in the process of attaching the pulse measurement unit 150 equipped with the bio-signal measurement device 140, which will be described later, have. In this way, the bio-signal measuring device 140 can receive the bio-signal from the bio-signal sensing electrode 130 by contacting the other end of the lead 124.

1, a variety of vital sign sensing electrodes 130 may be arranged in the living body signal measuring apparel 100. [ In addition, the detachable attachment point 126 may be disposed at any position of the non-conductive garment 120 other than the arm portion shown in Fig. In Fig. 1, three bio-signal sensing electrodes 130 arranged in a non-conductive clothing 120 are shown as an example. The two bio-signal sensing electrodes 130 of the three bio-signal sensing electrodes 130 are used for sensing a bio-signal, and the other bio-signal sensing electrode 130 is used as a reference electrode for providing a reference signal .

In one embodiment, the bio-signal sensing electrode 130 may include a second through hole 132 formed through the inside thereof. At this time, the skin 10 on which the conductive member 110 is disposed can communicate with the outside through the second through hole 132. The conductive member 110 may be obtained by coating the skin 10 through the second through hole 132 of the nonconductive garment 120 and then drying. At this time, the conductive material 110a may be coated on the skin 10 through the second through hole 132 and then dried, so that the conductive member 110 may face the bio-signal sensing electrode 130. [

The bio-signal measuring device 140 includes a health information analyzing unit 140a for analyzing the health information of the object from the bio-signal received from the bio-signal sensing electrode 130. In addition, the bio-signal measuring apparatus 140 may include an interface 144 disposed on the outside or inside. The health information analyzer 140a may provide the health information of the object to the external device 148 and may receive the health information of the object and the environment information of the object during the health information measurement from the external device 148 Can be provided. In addition, the bio-signal measuring apparatus 140 may include a housing 142a in which the health information analyzing unit 140a is embedded. The display 142 may be disposed on the outer surface or inside the housing 142a. When the display 142 is disposed inside, the housing may have a light-transmitting material. The health information analysis unit 140a may display the health information of the object on the display unit 142. [ At this time, the bio-signal measuring apparatus 140 includes a power measuring unit 150, a bio-signal detecting electrode 130, an interface unit 144, a power supply unit 146 for supplying power to the display and health information analyzing unit 140a, . For example, as shown in FIG. 2, the bio-signal measuring apparatus 140 may be mounted on the pulse measuring unit 150. At this time, the bio-signal measuring device 140 contacts the other end of the lead 124 in the process of attaching the pulse measuring part 150 to the detachable attachment point 126, and thereby the bio-signal measuring electrode 130 and the pulse measuring part 150 And the heartbeat signal, respectively.

The health information analysis unit 140a can generate the electrocardiographic waveform 134 of the object from the bio-signal. In addition, the health information analysis unit 140a may generate the pulse waveform 156 of the object from the pulse signal. At this time, the health information analysis unit 140a may detect one or more minutiae points of the pulse wave pattern 156. [ The health information analyzing unit 140a detects a time (hereinafter referred to as T_Rp) at which the peak value of the depolarization timing of the ventricle occurs from the generated electrocardiogram waveform 134, (Hereinafter referred to as " T_Hp "). At this time, the health information analysis unit 140a can extract the pulse wave propagation time 158 from T_Hp and T_Rp. The health information analysis unit 140a may calculate the blood pressure of the subject from the extracted pulse wave propagation time 158. [

The characteristic point of the pulse waveform 156 is a characteristic of the pulse waveform 156 that can occur in a specific section in the pulse waveform 156 repeated at a constant cycle.

As an example, the maximum point 156a of the pulse waveform 156 may be used as the minutiae of the pulse waveform 156, as shown in Fig. 5 (a). The maximum point 156a of the pulse waveform 156 may be defined as a point indicating the maximum value of the pulse wave 156 measured in the arterial blood vessel when the heart is contracted.

As another example, the lowest point 156b of the pulse waveform 156 may be used as the minutiae of the pulse waveform 156, as shown in Fig. 5 (b). The lowest point 156b of the pulse waveform 156 may be defined as the minimum point of the pulse waveform 156 during relaxation of the heart or the starting point of the initial rise of the pulse waveform 156 during the contraction of the heart.

As another example, the maximum point 156a of the pulse waveform 156 and the average point 156c of the lowest point 156b may be used as the minutiae of the pulse waveform 156, as shown in Fig. 5 (c) . The average point 156c of the pulse waveform 156 corresponds to about 50% of the total amplitude of the pulse waveform 156. The value of the maximum point 156a of the pulse waveform 156 during the contraction of the heart, It can be defined as a point where an average value of the minimum point of the pulse waveform 156 at the relaxation of the heart appears.

As another example, as the feature point of the pulse waveform 156 as shown in Fig. 5 (d), the first derivative 156 'maximum point 156d of the pulse waveform 156 may be used. The maximum point 156d of the first derivative 156 'of the pulse waveform 156 can be defined as a point having the maximum rate of rise in the pulse waveform 156 during the contraction of the heart. The primary differential 156 'maximum point 156d of the pulse waveform 156 is located at a point somewhat lower than the average point 156c or the average point 156c of the pulse waveform 156. [

As another example, as the feature point of the pulse waveform 156 as shown in FIG. 5 (e), the maximum point 156e of the second derivative 156 "of the pulse waveform 156 may be used. The maximum point 156e of the second derivative 156 " of the pulse waveform 156 is located around the base point (not shown) of the pulse waveform 156. The base point of the pulse waveform 156 refers to the point at which the pulse waveform 156 first reaches any point.

As another example, an intersection of a line tangent 156f of the pulse waveform 156 may be used as the characteristic point of the pulse waveform 156, as shown in Fig. 5 (f). The intersection 156f of one tangential line of the pulse waveform 156 is defined by the tangent 158a of the lowest point 156b of the pulse waveform 156 during relaxation of the heart and the second line of the pulse waveform 156 during the contraction of the heart And the tangent 158c of the maximum point 156e of the differential 156 ''.

As another example, an intersection of two line tangents 156g of the pulse waveform 156 may be used as the feature point of the pulse waveform 156, as shown in Figure 5 (g). The intersection 156g of the two tangential lines of the pulse waveform 156 causes the tangential line 158c of the second derivative 156''maximum point 156e at the time of contraction of the heart and the pulse wave form 156 And the tangential line 158b of the first derivative 156 'of the maximum point 156d at the point 156d.

Pulse transit time 158 (PTT) is the time that is passed from the aortic valve to the arterial vessel where the pulse measure is placed. The pulse wave propagation time 158 is the peak point of the R wave 134c of the electrocardiogram waveform 134 (hereinafter referred to as the R-peak 136) or the peak of the Q wave 134b (hereinafter referred to as the Q- ) Point) and the pulse waveform 156 may be defined as the time difference between any of the above-described minutiae points.

6, the health information analyzing unit 140a analyzes the R-peak point 136 of the ECG waveform 134 and the maximum point 156e of the second derivative 156 '' of the pulse waveform 156, ) May be defined as the pulse wave transmission time 158 to calculate the pulse wave transmission time 158.

The blood pressure of the subject may include systolic blood pressure and diastolic blood pressure. The systolic blood pressure can be calculated by applying the pulse wave transfer time 158 to the first regression equation. The diastolic blood pressure is applied to the second regression equation based on the systolic blood pressure, the pulse wave propagation time 158, the body characteristic information of the object, the electrocardiographic waveform 134, and the pulse wave form 156 measured .

The systolic blood pressure was measured by the pulse wave propagation time at the blood pressure equation (JC Bramwell and AVHill, Proceedings of the Royal Society, London, pp. 298-306, 1922) (158). ≪ / RTI > For example, the systolic blood pressure can be calculated by the first regression equation using the pulse wave transfer time 158 and the pulse wave transfer time 158 obtained through the general statistical analysis program for the systolic blood pressure as variables.

(First regression equation)

Systolic blood pressure = A1 * pulse wave transmission time + A2

Here, A1 to A2 are constants obtained through regression analysis, and additional factors other than the factors described for obtaining the systolic blood pressure may be used.

The diastolic blood pressure may be obtained by combining the systolic blood pressure, pulse wave transmission time 158, the body characteristic information of the object, the electrocardiographic waveform 134, and the environmental information measured during the measurement of the pulse wave form 156, Can be calculated by the above-described second regression equation.

The body characteristic information of the object may include at least one selected from a key, a body weight, a body fat percentage, a body fat, an arm circumference, an arm length, and a combination thereof.

The environmental information may include at least one of temperature, humidity, and air pressure.

(Second regression equation)

Systolic blood pressure = C1 * systolic blood pressure C2 * pulse wave transmission time + C3 * body characteristic information + C4 * environmental information + C5

Here, C1 to C5 are constants obtained through regression analysis, and additional factors other than the factors described for obtaining the diastolic blood pressure may be used.

The pulse measuring unit 150 may be disposed on the nonconductive garment 120 to face the arterial blood vessel. The pulse measuring unit 150 may analyze at least one selected from a change in external shape of the arterial blood vessel due to contraction and relaxation of the ventricle of the subject, a pressure change, a change in light absorption amount, The pulse signal of the object can be sensed. In addition, the pulse measuring unit 150 may provide the pulse signal of the object to the health information analyzing unit 140a.

In one example, the pulse measuring unit 150 may be detachably attached to and detached from the detachment point 126 of the non-conductive garment 120 shown in Fig. The pulse measuring unit 150 can be detached and attached to the nonconductive clothes 120. [ In this case, the bio-signal measuring device 140 can be attached to the pulse measuring part 150. At this time, the bio-signal measuring device 140 contacts the other end of the lead 124 in the process of attaching the pulse measuring part 150 to the detachable attachment point 126, and thereby the bio-signal measuring electrode 130 and the pulse measuring part 150 And the pulse signal, respectively. The pulse measuring unit 150 may calculate the blood pressure through the provided bio-signal and the pulse signal as described above. The pulse measuring part 150 may include a band part 152 surrounding the detachable attachment point 126 of the nonconductive garment 120. The band part 152 may fix the pulse measuring part 150 to the detachable attachment point 126 of the nonconductive garment 120 such that the pulse measuring part 150 faces the arterial blood vessel.

Various sensors may be used as the pulse measuring unit 150. [

As shown in FIG. 2, the pulse sensor 150 may be an optical sensor 154. 2, the light sensor 154 may include a light emitting portion 154b that emits light to the skin 10 of the object and a light receiving portion 154a that receives the emitted light. The light emitting portion 154b and the light receiving portion 154a may be spaced apart from each other. The optical sensor 154 may be opposed to the skin 10 of the subject, that is, the arterial blood vessel located under the skin 10 during the process of wearing the object. The amount of blood flowing through the arterial blood vessels depends on the contraction of the heart of the subject and the relaxation. The blood flowing through the arterial blood vessel can absorb a part of the light emitted from the light emitting portion 154b. Accordingly, the amount of the arterial blood vessel absorbing the light emitted from the light emitting portion 154b varies depending on the amount of blood flowing through the arterial blood vessel. A light receiving unit 154a receiving the light emitted from the light emitting unit 154b detects a change in the light absorption amount of the arterial blood vessel according to the change of the blood amount of the arterial blood vessel and outputs the sensed signal to the health information analyzing unit 140a ), So that the pulse waveform 156, the pulse rate, and the like can be measured from the change amount of the light absorption amount. As the light source used in the light emitting unit 154b, an infrared (IR) light source and a red light source may be used alone or in combination.

2, an impedance measuring unit (not shown) may be used as the pulse measuring unit 150. [ The impedance measuring unit senses a change in the electrical impedance due to the shrinkage of the heart and the change in cross-sectional area due to the relaxation.

For example, the impedance measuring unit may include a pair of current electrodes that provide current to the skin of the object, which are disposed to be spaced apart from each other, and a voltage (voltage) from the current supplied to the skin 10, And a pair of voltage electrodes for measuring the voltage. The health information analysis unit 140a can measure the pulse wave form 156, the pulse rate, and the like from the change amount of the electrical impedance.

As another example, the impedance measuring unit may be formed by integrating the pair of current electrodes and the pair of voltage electrodes into a pair of electrodes. The pair of electrodes may provide the current to the skin 10 of the object and may measure the voltage from the current provided to the skin 10. [ The health information analysis unit 140a can measure the pulse wave form 156, the pulse rate, and the like from the change amount of the electrical impedance.

2, a pressure sensor (not shown) may be used as the pulse measuring unit 150. [ The pressure sensor measures an absolute or relative pressure of the arterial blood vessel.

For example, a piezoresistive pressure sensor (not shown) may be used as the pressure sensor. The piezoresistive pressure sensor can take a diaphragm type, a cantilever structure, or the like. In addition, the piezoresistive pressure sensor can be manufactured by utilizing a Si wafer. The piezoresistive pressure sensor may comprise various types of silicon diaphragms and resistors formed on the diaphragm. The piezoresistive pressure sensor can sense a change in the pressure of the arterial blood vessel through a change in an electrical resistance value caused by a physical change of the pressure sensor structure due to a pressure change of the arterial blood vessel. The health information analyzing unit can measure a pulse wave form, a pulse rate, a heart rate, etc. from a change in the sensed electric resistance value.

As another example, a piezoelectric pressure sensor (not shown) may be used as the pressure sensor. The piezoelectric type pressure sensor may be of a piezoelectric type having a thin film of a material having a piezoelectricity property. As the electric field due to the polarization of the MOSFET changes from the pressure change of the arterial blood vessel, the piezoelectric type pressure sensor senses a change in the charge of the MOSFET or a potential difference across the MOSFET, The health information analyzing unit 140a to measure the pulse waveform 156 and the heart rate from the change amount of the electric charge or the electric potential difference.

As another example, a capacitive pressure sensor (not shown) may be used as the pressure sensor. The capacitive pressure sensor may include a first substrate disposed opposite to the arterial blood vessel, and a second substrate spaced apart from the first substrate. Wherein the capacitance type pressure sensor senses a change in capacitance as the distance between the first substrate and the second substrate becomes closer to the pressure change of the arterial blood vessel and outputs the sensed signal to the health information analysis unit 140a to measure the pulse waveform 156 and the heart rate from the change amount of the capacitance.

The conductive material supply unit 160 may receive the conductive material 110a therein. 3, a conductive material 110a is accommodated in the conductive material supply unit 160 and an opening 160b through which the conductive material 110a can be discharged by an applied external force 12, A diffusion plate 162 disposed opposite to the opening portion 160b and a connection portion 164 connecting the container 160a and the diffusion plate 162. [ For example, the conductive material 110a may be discharged through the opening 160b through the process of inserting the opening 160b into the second through hole 132 and then applying the external force 12 to the container 160a. have. At this time, the conductive material 110a is diffused by the diffusion plate 162 in the discharging process, is provided to the skin 10, and then dried. Thereby, the conductive member 110 is self-aligned with the bio- Or the like.

For example, the diffuser plate 162 may have a plate shape. The plate shape may be various shapes such as a disk shape, a polygonal plate shape, and the like. The conductive material supplied through the opening 160b may be diffused by being scattered through the edge of the diffusion plate 162 after colliding with the diffusion plate 162. [

As another example, the diffusion plate 162 may have a plate shape having a third through hole (not shown) therein. The plate shape may be various shapes such as a disk shape, a polygonal plate shape, and the like. The conductive material 110a supplied through the opening 160b may be scattered through the edge of the diffusion plate 162 after colliding with the diffusion plate 162 and being discharged downward through the through hole. On the other hand, a plurality of protrusions (not shown) may be formed on the surface of the diffusion plate 162 facing the opening 160b. The plurality of protrusions help the conductive material 110a supplied through the opening portion 160b against the conductive material 110a supplied through the opening portion 160b to be scattered more evenly to the edge of the diffusion plate 162 And the like. At least one of the plurality of protrusions may be disposed immediately below the opening 160b and may have a conical or polygonal conical shape so that the conductive material 110a supplied through the opening 160b contacts the edge of the diffusion plate 162 It is possible to perform the role of being distributed evenly.

In other words, the bio-signal measuring apparel 100 disclosed in this specification includes a pulse measuring unit 150, and the pulse signal of the object sensed by the pulse measuring unit 150 is supplied to the bio- / RTI > The bio-signal measuring device 140 may calculate the blood pressure of the object from the pulse signal provided from the pulse measuring unit 150 and the electrocardiogram signal provided from the bio-signal sensing electrode 130, and may inform the object of the blood pressure . Accordingly, the bio-signal measurement apparel 100 disclosed in this specification can provide the effect that the object can self-measure the blood pressure of the subject.

7 is a view showing a bio-signal measurement apparel disclosed in this specification according to another embodiment.

The bio-signal measurement apparel 200 includes a conductive member 110, a nonconductive apparel 120, a bio-signal sensing electrode 130, a bio-signal measurement device 140, and a pulse measurement unit 150 do. In some other embodiments, the bio-signal measurement apparel 200 may optionally further include a conductive material supply 160

For the sake of convenience of description, the description of the substantially same elements in the description of the elements described above will be omitted.

In another embodiment, the nonconductive garment 120 can be modified in structure as shown in Fig.

The nonconductive garment 120 may extend to face at least one of the wrist, ankle, neck, and combinations thereof, referred to below as a pulse measuring point.

The pulse measuring part 150 is disposed in the nonconductive garment 120 so as to face the arterial blood vessel at the pulse measuring point.

7 shows an example of a biological signal measurement apparel 200 in which two bio-signal sensing electrodes 130 are disposed. In FIG. 7, two conductive lines 124 each having one end connected to the two bio-signal sensing electrodes 130 are illustrated as an example. In this case, the other ends of the two conductors 124 may be connected to each other with a detachable attachment point 126, which is disposed at the sleeve portion, ankle portion or neck portion of the non-conductive garment 120, respectively. The biosignal sensed by the bio-signal sensing electrode 130 may be provided to the detachment / attachment point 126 through the lead 124. In addition, the pulse measuring unit 150 may be disposed in the sleeve portion of the nonconductive garment 120 to sense a pulse signal from the radial artery. In addition, the pulse measuring unit 150 can detect the pulse signal even when the other part due to physiological shock or cardiac arrest is not promoted from the carotid artery by being disposed in the neck of the non-conductive garment 120. The pulse measuring unit 150 may also be disposed at the ankle portion of the non-conductive garment 120 to sense the pulse signal from the posterior tibial artery.

7, the bio-signal measuring apparel 200 may be provided with various numbers of the bio-signal detecting electrodes 130. FIG. The attachment / detachment point 126 may also be disposed at any location on the non-conductive garment 120 that is not the ankle portion, the sleeve portion of the non-conductive garment 120.

In other words, when the deformed nonconductive clothes 120 shown in FIG. 7 are utilized, the bio-signal sensing electrode 130 senses the bio-signals in a low contact resistance environment through the conductive member 110 disposed on the skin can do. In addition, the pulse measuring unit 150 may be disposed on the sleeve portion, the ankle portion, or the neck portion of the non-conductive garment 120 so as to sense the pulse signal of the object in an emergency as well as a normal state. The pulse signal of the subject sensed by the pulse measuring unit 150 is provided to the bio-signal measuring device 140. [ The bio-signal measuring apparatus 140 may calculate the blood pressure of the object from the pulse signal provided from the pulse measuring unit 150 and the electrocardiogram signal provided from the bio-signal sensing electrode 130, and inform the object of the blood pressure. Accordingly, the bio-signal measuring apparel 200 can provide the effect that the object can self-measure the blood pressure of the subject.

From the foregoing it will be appreciated that various embodiments of the present disclosure have been described for purposes of illustration and that there are many possible variations without departing from the scope and spirit of this disclosure. And that the various embodiments disclosed are not to be construed as limiting the scope of the disclosed subject matter, but true ideas and scope will be set forth in the following claims.

10: Skin
12: External force
100, 200: Measurement of biological signals Clothing
110: conductive member
110a: Conductive material
120: Non-Conductive Clothes
122: first through hole
124: lead
126: attachment point
130: Biological signal sensing electrode
132: second through hole
134: ECG waveform
134a: P wave
134b: Q wave
134c: R wave
134d: S wave
134e: T wave
136: R-peak point
140: Biosignal measuring device
140a: Health Information Analysis Department
142:
144:
146:
148: External device
150: Pulse measuring part
152: band part
154: Light sensor
154a:
154b:
156: Pulse waveform
156 ': First differential of pulse waveform
156 ": Second derivative of pulse waveform
156a: maximum point
156b: lowest point
156c: Average point
156d: First derivative maximum point
156e: Second derivative maximum point
156f: intersection of one tangent
156g: intersection of two tangents
158a: tangent to lowest point
158b: Tangent to the first derivative maximum point when the heart relaxes
158c: Tangent to the second derivative peak at the contraction of the heart
158: pulse wave propagation time
160: Conductive material supply unit
160a: container
160b: opening
162: diffuser plate
164:

Claims (9)

A conductive member disposed on the skin of the object; And
And a biosignal sensing electrode disposed in the nonconductive garment to be worn by the object and capable of sensing the biosignal in electrical contact with the conductive member continuously or intermittently according to the movement of the object,
Wherein the bio-signal sensing electrode is connected to the bio-signal measurement device to provide the bio-signal to the bio-signal measurement device,
The bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal received from the bio-signal detecting electrode,
Wherein the nonconductive clothing includes a first through hole formed adjacent to the bio-signal sensing electrode,
Wherein the conductive member is formed by coating a conductive material having fluidity on the skin through the first through hole and then drying the conductive material to face the bio-signal sensing electrode,
The conductive material is brought into close contact with the surface of the skin due to the fluidity in the process of coating the skin, so that the contact resistance between the conductive member and the skin is reduced so that the bio-signal sensing electrode senses the bio- Can measure vital signs clothing. A conductive member disposed on the skin of the object; And
And a biosignal sensing electrode disposed in the nonconductive garment to be worn by the object and capable of sensing the biosignal in electrical contact with the conductive member continuously or intermittently according to the movement of the object,
Wherein the bio-signal sensing electrode is connected to the bio-signal measurement device to provide the bio-signal to the bio-signal measurement device,
The bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal received from the bio-signal detecting electrode,
Wherein the bio-signal sensing electrode includes a second through-hole formed through the inside thereof,
The skin on which the conductive member is disposed communicates with the outside through the second through hole,
Wherein the conductive member is formed by coating a conductive material having fluidity on the skin through the second through hole and then drying the conductive material to face the bio-signal sensing electrode,
The conductive material is brought into close contact with the surface of the skin due to the fluidity in the process of coating the skin, so that the contact resistance between the conductive member and the skin is reduced so that the bio-signal sensing electrode senses the bio- Can measure vital signs clothing. 3. The method according to claim 1 or 2,
And a pulse measuring unit disposed in the nonconductive garment,
Wherein the pulse measuring portion is disposed in the nonconductive garment so as to face the arterial blood vessel,
Wherein the pulse measuring unit analyzes at least any one of a change in external shape of the arterial blood vessel caused by contraction and relaxation of the heart of the subject, a pressure change, a change in light absorption amount, Lt; / RTI >
Wherein the pulse signal of the subject sensed by the pulse measurement unit is provided to the health information analysis unit and the health information analysis unit analyzes the health information of the subject from the bio signal and the pulse signal. A conductive member disposed on the skin of the object;
Conductive clothing that is worn by the object and extends to face at least one of the wrists, ankles, necks, and combinations thereof, referred to as a pulse measuring point, of the object, A living body signal sensing electrode capable of continuously or intermittently contacting the conductive member to sense a living body signal; And
Wherein the arterial blood vessel is disposed in the nonconductive garment so as to oppose the arterial blood vessel of the pulse measurement point, the change of the outer shape of the arterial blood vessel, the pressure change, the change of the light absorption amount, and the electrical characteristic of the pulse measurement point due to the contraction and relaxation of the heart of the object And a pulsation measuring unit for analyzing at least one of the pulsation of the subject and the pulsation signal of the subject,
Wherein the bio-signal detecting electrode and the pulse measuring unit are respectively connected to the bio-signal measuring device to provide the bio-signal and the pulse signal to the bio-signal measuring device,
Wherein the bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal and the pulse signal,
Wherein the nonconductive clothing includes a first through hole formed adjacent to the bio-signal sensing electrode,
Wherein the conductive member is formed by coating a conductive material having fluidity on the skin through the first through hole and then drying the conductive material to face the bio-signal sensing electrode,
The conductive material is brought into close contact with the surface of the skin due to the fluidity in the process of coating the skin, so that the contact resistance between the conductive member and the skin is reduced so that the bio-signal sensing electrode senses the bio- Can measure vital signs clothing. A conductive member disposed on the skin of the object;
Conductive clothing that is worn by the object and extends to face at least one of the wrists, ankles, necks, and combinations thereof, referred to as a pulse measuring point, of the object, A living body signal sensing electrode capable of continuously or intermittently contacting the conductive member to sense a living body signal; And
Wherein the arterial blood vessel is disposed in the nonconductive garment so as to oppose the arterial blood vessel of the pulse measurement point, the change of the outer shape of the arterial blood vessel, the pressure change, the change of the light absorption amount, and the electrical characteristic of the pulse measurement point due to the contraction and relaxation of the heart of the object And a pulsation measuring unit for analyzing at least one of the pulsation of the subject and the pulsation signal of the subject,
Wherein the bio-signal detecting electrode and the pulse measuring unit are respectively connected to the bio-signal measuring device to provide the bio-signal and the pulse signal to the bio-signal measuring device,
Wherein the bio-signal measuring apparatus includes a health information analyzing unit for analyzing health information of the object from the bio-signal and the pulse signal,
Wherein the bio-signal sensing electrode includes a second through-hole formed through the inside thereof,
The skin on which the conductive member is disposed communicates with the outside through the second through hole,
Wherein the conductive member is formed by coating a conductive material having fluidity on the skin through the second through hole and then drying the conductive material to face the bio-signal sensing electrode,
The conductive material is brought into close contact with the surface of the skin due to the fluidity in the process of coating the skin, so that the contact resistance between the conductive member and the skin is reduced so that the bio-signal sensing electrode senses the bio- Can measure vital signs clothing. The method according to claim 4 or 5,
Wherein the health information analyzer generates an electrocardiogram waveform of the object from the bio signal and generates a pulse waveform of the object from the pulse signal and the health information analyzer detects one or more minutiae points of the pulse waveform,
The health information analyzing unit detects a time when a peak value of the ventricular depolarization timing occurs from the generated electrocardiographic waveform - hereinafter referred to as T_Rp, and a time at which the feature point detected from the pulse waveform is generated - hereinafter referred to as T_Hp Extracting the pulse wave transmission time from the T_Hp and the T_Rp, and calculating the blood pressure of the object based on the extracted pulse wave transmission time. The method according to claim 6,
Wherein the blood pressure of the subject includes systolic blood pressure and diastolic blood pressure,
Wherein the systolic blood pressure is calculated by applying the pulse wave transmission time to a first regression equation,
Wherein the diastolic blood pressure is calculated by applying the pulse wave transmission time, the body characteristic information of the object, the electrocardiographic waveform, and the environment information measured in the measurement of the pulse wave waveform to a second regression equation. The method according to claim 4 or 5,
Wherein the bio-signal sensing electrode is disposed in the non-conductive garment in such a manner as to woven conductive fibers in the non-conductive garment,
Wherein the bio-signal measuring device is mounted on the pulse measuring part,
Wherein the pulse measuring unit is detachably attached to the nonconductive garment,
The nonconductive garment includes a lead extending to a corresponding point of the non-conductive garment, one end of which is electrically connected to the bio-signal sensing electrode, and the other end of which is detachably attached to the non-conductive garment,
The conductive wire being formed by weaving conductive fibers in the non-conductive garment,
The living body signal measuring device may be provided with the living body signal and the pulse signal from the living body signal detecting electrode and the pulse measuring unit by being brought into contact with the other end of the lead in the process of attaching the pulse measuring unit to the detachable attachment point Measuring the biological signal in the clothing. 6. The method according to claim 2 or 5,
Further comprising a conductive material supplier for receiving the conductive material,
The conductive material supply unit
A container accommodating the conductive material therein and having an opening through which the conductive material can be discharged by an applied external force;
A diffusion plate disposed opposite to the opening; And
And a connection part connecting the container and the diffusion plate,
The conductive material is discharged through the opening through the process of inserting the opening into the second through hole and then applying the external force to the container,
Wherein the conductive material is diffused by the diffusion plate in the discharging process, is provided on the skin, and then dried, so that the conductive member is disposed in a self-aligning manner so as to be opposed to the living body signal sensing electrode.

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