KR100964286B1 - Method and system for measuring heart activity - Google Patents

Abstract

Methods and systems for measuring cardiac activity are disclosed. The electrode patch according to the present invention is formed through the adhesive portion, the adhesive portion, three electrodes respectively disposed at the vertex position of the triangle to detect the biopotential signal and the peripheral region of each of the electrodes exposed on the bottom surface of the adhesive portion It includes an electrolyte region is formed by applying the electrolyte. According to the present invention, it is possible to prepare for a ubiquitous care environment by providing a miniaturized cardiac activity measuring device so that a user can measure cardiac activity anytime and anywhere.

Vital signs, heart, electrodes

Description

Method and system for measuring heart activity

FIELD OF THE INVENTION The present invention relates to cardiovascular system diagnostics, and more particularly, to methods and systems for measuring cardiac activity.

Measurement of heart activity is performed to check for abnormalities in the heart and to test for heart disease (eg, angina pectoris, myocardial infarction, arrhythmia, etc.).

In general, the electrode induction method used in the clinic to measure the electrical abnormality of the heart occurs when the electrical stimulation generated in the sagittal node (SA node) of the heart is conducted to the left and right ventricle (Arium) and the left and right atrium (Ventricles). By measuring biopotential, two or more electrodes are attached to the human body surface for measurement.

In addition, in order to measure the electrical activity of the heart on the body surface, it is possible to measure the high voltage as the measurement distance increases, so the existing clinical electrocardiograph is used for the right hand (RA), left hand (LA), and left leg as far from the heart as possible. It consists of measuring the voltage differentially at (LF).

As described above, the limb electrode induction method (Standard Limb) and the two-electrode measurement method are mainly used as a measuring method using an electrode. Depending on the position of the electrode attached to the subject's body, it is typically classified into LEAD I, LEAD II, and LEAD III. Electrode attachment method and specific electrocardiogram measurement method according to LEAD I, II and III are conventionally used and the description thereof is omitted.

1 is a view showing a cardiac activity measuring method using a limb electrode induction method according to the prior art.

Electromagnetically, the longer the path of the line integral (long integral), the greater the potential can be measured, as shown in Figure 1 according to the limb electrode induction method electrodes on both arms and legs of the human body (110-1) To 110-4), and each electrode is connected to the measuring device 130 through each of the cables 120-1 to 120-4 to measure electrical activity of the heart.

The limb electrode induction method is difficult to miniaturize, has a disadvantage of being sensitive to noise, and since it is inconvenient to use in a mobile environment because a connection between each electrode and a cable is required, it is mainly used for clinical use.

In addition, the electrode is attached using an electrolytic gel in consideration of contact resistance between the electrode and the skin, but when used for a long time, the distortion of the biosignal increases rapidly due to the polarization phenomenon inside the gel. Therefore, there is a disadvantage that the measurement should be made within a certain time after the electrode is attached and the electrode should be attached again after the elapse of time. In addition, the distance between the electrodes must be secured at least 10 cm or more can be a normal signal measurement.

On the other hand, a technique for minimizing the limb electrode induction method is configured to be used during the movement is also being developed. For example, Patent Registration No. 10-356421, entitled "Portable Electrocardiogram Measuring Device," filed June 12, 2000 and registered on September 30, 2002, by Bionet Corporation, discloses such a portable electrocardiogram measuring device. It is starting.

However, the electrocardiogram measuring apparatus disclosed in Patent Registration No. 10-356421 is intended for use by a doctor during mobile medical care, and is not intended to be attached to a body by a patient and to measure electrical activity of the heart during daily life.

In particular, the electrical measurement of cardiac activity in such a daily environment is not the level of cardiac electrical activity measurement for diagnosis by a specialist such as a doctor, and therefore, two-electrode measurement is often used to measure heart activity such as heart rate.

2 is a view showing a cardiac activity measuring method using a two-electrode method according to the prior art.

As shown in FIG. 2, the two-electrode method allows the chest region to be pressed using a rubber band 140 or the like to reduce the measurement error caused by movement during movement, and two electrodes 110-5 in the rubber band 140. And 110-6 on the left and right sides of the heart, and are connected to the measuring device 130 via cables 120-5 and 120-6.

However, even when the chest region is pressed by the rubber band 140, when the movement against the gravity or the movement of a severe heart region such as severe breathing occurs, the electrode moves. In addition, since the two-electrode method also strongly presses the heart area with the rubber band 140 to attach the electrode, it is impossible to use it for a long time, and it is impossible to use it for clinical use simply by measuring the heart rate, and simply evaluates the performance or exercise load. There is a limit that can be used only within the limited range of the above.

In order to solve the above-described problems, the present invention is to provide a cardiac activity measuring device that can be miniaturized so that the user can measure cardiac activity anytime, anywhere in order to prepare for the ubiquitous care environment.

It is also an object of the present invention to provide a method and system for measuring cardiac activity that enables the selection of an accurate measurement location to obtain a measurement waveform that is the same or very similar to a clinical electrocardiogram that a clinician can interpret cardiac activity.

In addition, the present invention is to provide a cardiac activity measuring method and system that can minimize the inconvenience of measuring the heart activity of the subject, and can remove the dynamic noise by a wired cable connecting between the electrode and the measuring device.

In addition, the present invention is to provide a method and system for measuring cardiac activity that transmits the measured cardiac activity information to the outside to enable ubiquitous telemedicine.

In addition, the present invention can efficiently monitor the state of the cardiovascular system by measuring cardiac activity and / or electronic stethoscope, and can remotely check the health status of the subject on a regular basis based on the monitored data, if it is determined to be a risk It is to provide a method and system for measuring cardiac activity that can notify a subject or the like.

Other objects of the present invention will be easily understood through the following description.

Electrode patch according to an embodiment of the present invention, the adhesive portion formed through the adhesive portion, and exposed to the three electrodes and the bottom surface of the adhesive portion respectively disposed at the vertex position of the triangle to detect the biopotential signal The electrolyte may include an electrolyte region formed by applying an electrolyte to a peripheral region of each of the electrodes.

Two of the three electrodes may be used to receive a biopotential signal for differential amplification, and the other electrode may be used as a reference electrode.

The two electrodes for receiving a biopotential signal may be arranged for LEAD II measurement.

A medical adhesive may be applied to the bottom of the adhesive portion. The three electrolyte regions may be arranged to be spaced apart from each other.

The adhesive portion may be formed with one or more holes. The holes can be used for sweat release or sensor exposure.

According to another embodiment of the present invention, a sensing device includes three electrode electrodes disposed through an adhesive part, and an electrode patch part formed by applying an electrolyte to a peripheral region of each electrode on a bottom surface of the adhesive part; It may include a signal processing unit coupled to the electrode patch unit for transmitting a signal generated by amplifying the biopotential signal input through the electrode to the terminal device in a wireless communication method.

The electrode patch unit and the signal processor may be coupled in a snap button manner.

The electrode patch part is formed through the adhesive part, the adhesive part, and three electrodes respectively disposed at vertex positions of a triangle to detect a biopotential signal, and a peripheral region of each of the electrodes exposed at the bottom surface of the adhesive part. It may include an electrolyte region formed by applying an electrolyte (electrolyte) to.

The signal processor may include: an amplifier for amplifying a biopotential signal input through the electrode; an A / D converter for converting the amplified biopotential signal into a digital signal; and converting the amplified digital signal into a wireless signal format. It may include a communication performing unit for transmitting to the terminal device in a communication method.

Alternatively, the signal processor may include: an amplifier for amplifying a biopotential signal input through the electrode; a filtering unit for removing a noise component from the amplified biopotential signal; an A / D for converting the filtered biopotential signal into a digital signal The converter analyzes the biopotential signal converted into a digital signal and extracts data on the electrical activity of the heart, and converts the extracted data into a wireless signal format and transmits the data to the terminal device in a wireless communication method. It may include wealth.

One or more holes may be formed in the adhesive portion. In this case, the signal processor includes a sensor unit including sensing means disposed in contact with or close to the skin surface through the hole. An amplifier unit amplifies a biopotential signal input through the electrode. A filtering unit for removing the A / D conversion unit for converting the filtered biopotential signal into a digital signal by analyzing the sensing signal detected by the sensor unit and the biopotential signal converted into a digital signal to obtain data on the electrical activity of the heart The apparatus may include a signal analyzing unit to extract and a communication performing unit converting the extracted data into a wireless signal format and transmitting the extracted data to the terminal device in a wireless communication method. The signal processor may further include a display unit configured to display information about an operation state of the sensing device and one or more of the extracted data.

The sensing means may be at least one of a body temperature sensor and a sound collection sensor.

Two of the three electrodes may be used to receive a biopotential signal for differential amplification, and the other electrode may be used as a reference electrode.

The two electrodes for receiving a biopotential signal may be arranged for LEAD II measurement.

A medical adhesive may be applied to the bottom of the adhesive portion. The three electrolyte regions may be arranged to be spaced apart from each other.

The present invention has the effect of being able to prepare for the ubiquitous care environment by providing a miniaturized cardiac activity measuring device so that the user can measure cardiac activity anytime, anywhere.

In addition, the present invention has the effect of obtaining a measurement waveform that is the same or very similar to the clinical electrocardiogram, by which the clinician can decode the cardiac activity by the selection of the correct measurement position.

In addition, the present invention has the effect of minimizing the inconvenience in measuring the heart activity of the subject, and can remove the dynamic noise by the wired cable connecting the electrode and the measuring device.

In addition, the present invention has the effect of enabling the ubiquitous telemedicine by transmitting the measured cardiac activity information to the outside.

In addition, the present invention can efficiently monitor the state of the cardiovascular system by measuring the cardiac activity and / or electronic stethoscope, and can remotely check the health state of the subject periodically based on the monitored data, if it is determined to be a risk It is also effective to notify a subject or the like.

As the invention allows for various changes and numerous embodiments, particular embodiments will be illustrated in the drawings and described in detail in the written description. However, this is not intended to limit the present invention to specific embodiments, it should be understood to include all transformations, equivalents, and substitutes included in the spirit and scope of the present invention. In the following description of the present invention, if it is determined that the detailed description of the related known technology may obscure the gist of the present invention, the detailed description thereof will be omitted.

The terms first, second, etc. may be used to describe various components, but the components should not be limited by the terms. The terms are used only for the purpose of distinguishing one component from another.

The terminology used herein is for the purpose of describing particular example embodiments only and is not intended to be limiting of the present invention. Singular expressions include plural expressions unless the context clearly indicates otherwise. In this application, the terms "comprise" or "have" are intended to indicate that there is a feature, number, step, operation, component, part, or combination thereof described in the specification, and one or more other features. It is to be understood that the present invention does not exclude the possibility of the presence or the addition of numbers, steps, operations, components, components, or a combination thereof.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings.

3 is a view schematically showing the configuration of the cardiac activity measurement system according to an embodiment of the present invention, Figure 4 is a block diagram showing a block configuration of a signal processing unit according to an embodiment of the present invention. 5 is a bottom view illustrating the shape of an electrode patch unit according to an exemplary embodiment of the present invention, and FIG. 6 is a cross-sectional view illustrating a shape of a sensing device in which an electrode patch unit and a signal processor are coupled according to an embodiment of the present invention.

As shown in FIG. 3, the cardiac activity measuring system is amplified after receiving and amplifying a biopotential signal from an electrode patch unit 310 and an electrode patch unit 310 attached to a surface of a human body to detect a biopotential signal. The signal processor 320 wirelessly transmits the potential signal to the outside, and the terminal device 330 which receives the signal transmitted wirelessly from the signal processor 320 and outputs it as visual information.

The electrode patch 310 and the signal processor 320 may be assembled by a coupling method of a snap button and attached to the body surface of the examinee in an integrated form.

The terminal device 330 may be provided with a software program that interprets the wireless signal received from the signal processor 320 and displays the visual information. Here, the visual information may be one or more of an electrocardiogram waveform corresponding to a biopotential signal detected on the body surface to which the electrode patch 310 is attached, or general information on heart activity interpreted by the electrocardiogram waveform. In addition, the terminal device 330 may receive a radio signal from the signal processor 320, and may be applied without limitation as long as it is an electric / electronic device capable of installing and operating the above-described software program. For example, a mobile phone or a PDA (Personal Digital Assistant), desktop computer, notebook computer and the like.

Referring to FIG. 4, the signal processor 320 may include an amplifier 410, an A / D converter 420, and a communicator 430.

As illustrated in FIG. 5, the amplifying unit 410 may use two electrodes 530-1 and 530-3 of the three electrodes 530-1, 530-2, and 530-3 arranged in the shape of a triangle vertex. The biopotential signals (V1, V2) input through the differential amplification. In this case, the biopotential signal may be input through a buffer (not shown), and one of the three electrodes 530-2 may remove a common signal component between the V1 and V2 signals and may perform a differential ( Differential) can be used as a reference electrode to remove EMI noise by measuring signal components.

The A / D converter 420 converts the amplified biopotential signal into a digital signal and outputs it, and the communication performing unit 430 converts the biopotential signal converted into a digital signal into a signal for wireless transmission and wirelessly transmits the signal. . In this case, a signal for wireless transmission may be temporarily stored in a storage unit (not shown) and then wirelessly transmitted.

5 is a bottom view illustrating the shape of the electrode patch part 310.

As shown in FIG. 5, the bottom shape of the electrode patch portion 310 includes an adhesive portion 510 for attaching to the skin surface, and three electrolyte regions 520-applied in an arc shape. 1, 520-2, and 520-3 and each electrode 530-1, 530-2, and 530-3 exposed to a portion of each electrolyte region 520.

The adhesive part 510 is for attaching the electrode patch part 310 to the surface of the human skin, and may be formed of, for example, one or more of a nonwoven fabric, a woven fabric, a cotton fabric, and a paper.

Each electrode may be disposed at each vertex position of a triangle (eg, an equilateral triangle, etc.), and two electrodes 530-1 and 530-3 for sensing a biopotential signal are disposed in the LEAD II direction.

As shown in FIG. 6, the electrode 530 is formed to have a convex protruding portion penetrating through the adhesive portion 510, and the protruding portion is combined with an accommodating portion formed in a concave shape in the signal processing unit 320. That is, the electrode patch part 310 and the signal processor 320 may be coupled by a snap button coupling method by the protrusion molding part. Here, the protruding part may be formed of the same material as that of the electrode 530, or may be implemented as a housing having a different material formed to penetrate the electrode therein.

As described above, by allowing the electrode patch portion 310 and the signal processing portion 320 to be coupled in a snap button coupling manner, the electrode patch portion 310 can be consumable for one-time use or several times, while the signal The processor 320 may be configured to be used repeatedly and / or long term.

In the bottom surface of the electrode patch portion 310, the electrolyte regions 520-1, 520-2, and 520-3 and the regions of the adhesive portion 510 that are not occupied by the electrodes 530-1, 530-2, and 530-3 are formed. Medical adhesives may be applied to all or part of the article to enhance adhesion between human skin and nonwovens. The medical adhesive can be, for example, a silicone gel.

The electrolyte applied around each electrode is used to solve a problem that may occur when an electrode, which is a metal, comes into contact with the skin surface of the human body. For example, the electrolyte may be used to reduce the contact resistance upon contact with the skin surface. .

The electrolyte regions 520-1, 520-2, and 520-3 spaced apart from each other in an arc shape may be formed to have the same circle diameter. It is apparent that the circle diameter for arranging the electrolyte regions 520-1, 520-2, and 520-3 may be selected from, for example, 20 to 40 mm, and other values. For reference, as the circle diameter decreases, a gain for differential amplification must increase, and noise may also be amplified, and thus a circuit for processing the same may be complicated. On the contrary, as the circle diameter increases, the gain for the differential amplification may be reduced, but the surface of the human body may be bent, so that the surface contact resistance at each electrode may vary, and thus noise may be generated.

In addition, by forming a gap between the electrolyte regions 520-1, 520-2, and 520-3, the sweat discharged to the surface of the human body when the electrode patch 310 is attached to the outside of the electrode patch 310 more easily. Can be discharged. Thereby, the adhesive force of the electrode patch part 310 can be kept excellent for a long time.

7 is a diagram illustrating a detailed configuration of a signal processor according to another exemplary embodiment of the present invention.

Referring to FIG. 7, the signal processor 320 may include an amplifier 410, a filter 710, an A / D converter 420, a signal analyzer 720, and a communication performer 430. have.

The amplifier 410 differentially amplifies the biopotential signals V1 and V2 input through two electrodes 530-1 and 530-3 of the three electrodes 530-1, 530-2, and 530-3. To print.

The filtering unit 710 removes unnecessary components (eg, noise components) from the signals amplified and input by the amplifier 410.

The A / D converter 420 converts the biopotential signal filtered by the filter 710 into a digital signal and outputs the digital signal.

The signal analyzer 720 analyzes the biopotential signal converted into the digital signal and extracts data representing the electrical activity of the heart. The data extracted by the signal analyzer 720 may be information for showing an electrocardiogram waveform, etc. In addition, the signal analyzer 720 may perform a processing operation for extracting various data for analyzing cardiac activity. The program or algorithm for the processing may be implemented and stored in advance.

The communication performing unit 430 converts the data extracted by the signal analyzing unit 720 into a signal for wireless transmission, and then wirelessly transmits the data to the terminal device 330. In this case, a signal for wireless transmission may be temporarily stored in a storage unit (not shown) and then wirelessly transmitted.

8 is a view showing a detailed configuration of a signal processing unit according to another embodiment of the present invention, Figure 9 is a bottom view showing the shape of the electrode patch portion according to another embodiment of the present invention.

Referring to FIG. 8, the signal processor 320 may include an amplifier 410, a filter 710, an A / D converter 420, a signal analyzer 720, a communication performer 430, and a sensor unit ( 810, a storage unit 820, and an output unit 830 may be included.

The signal analyzer 720 further analyzes the sensing signal input from the sensor unit 810 to extract data representing the electrical activity of the heart.

The sensor unit 810 may include, for example, any one of a body temperature sensor, a sound collection sensor, and the like, and the sensor may be disposed in direct contact with or close to the skin surface through the hole 910 illustrated in FIG. 9. have. 9 illustrates a circular shape in the shape of the hole 910, it will be apparent to those skilled in the art that the hole may be formed in various shapes as necessary. The hole 910 may be used for the purpose of discharging sweat even if the sensor unit 810 is not used to directly contact or close to the skin surface.

In addition, although FIG. 9 illustrates an electrode patch portion 310 in which one hole 910 is formed with respect to the center area of the bonding portion 510, one or more holes are formed at various positions of the bonding portion 510 (for example, Obviously, the inside of the electrolyte region and / or the outer portion may be formed on the center region of the adhesive portion 510.

For example, when the sensor unit 810 includes a sound collecting sensor, the sound collecting sensor may be disposed to contact or approach the surface of the skin to collect a stethoscope sound. That is, the diagnostic apparatus may provide a variety of cardiac activity information by allowing the diagnostic device to collect and analyze a stethoscope sound such as a heartbeat as well as an electrical activity signal of the heart. In this case, the sensor unit 810 may further include a sound collecting plate formed in the form of a cone or hemisphere, or a combination thereof, in order to more effectively collect the heartbeat, and for converting sound into an electrical signal. It may also include a small microphone.

The storage 820 stores the data analyzed by the signal analyzer 720. The output unit 830 may include one or more LEDs for indicating whether the signal processing unit and / or the sensing device is normally operating, a display unit for displaying information corresponding to the data analyzed by the signal analyzer 720, and the like. It may include.

In addition, although not shown, the signal processor 320 may be implemented in a form in which the sensor unit 810 is added to the configuration of FIG. 4. In this case, the information sensed by the sensor unit 810 may be wirelessly transmitted to the terminal device 330 through the communication performing unit 430, and may be analyzed by the terminal device 330.

10 is a bottom view showing the shape of the electrode patch according to another embodiment of the present invention.

As shown in FIG. 10, the external shape of the electrolyte regions 520-1, 520-2, and 530-3 applied around the electrodes 530-1, 530-2, and 530-3 is limited to an arc shape. However, the expanded form of the electrolyte region may be formed to form a specific figure (eg, triangle, square, star, etc.).

Similarly, it is apparent that the shape of each electrolyte region and / or the overall shape in which each electrolyte region is expanded may be formed in an amorphous shape instead of a specific figure.

FIG. 11 is a view schematically showing the location of general chest leads (Precordial leads, Chest leads), FIG. 12 is a view illustrating waveforms of a general clinical electrocardiogram, and FIGS. 13 to 18 are views according to an embodiment of the present invention. In the case where the sensing device is attached to each chest induction position is a view showing the ECG waveform at each position, Figure 19 is a correlation diagram between the waveform and the clinical electrocardiogram at each chest induction position to which the measurement device according to an embodiment of the present invention Is a comparison graph.

As illustrated in FIG. 11, to obtain six chest inductions, an anode is placed at six different places around the chest. Thoracic induction is projected through the atrioventricular node to the dorsal side of the patient as the cathode.

The location of thoracic induction is V1, the right sterna border of the fourth intercostal space, V2, the left sternum margin of the fourth intercostal space, V3, the middle of V2 and V4, and V4, where the fifth intercostal and left clavicle centerlines meet. , V6 is the total liquid and part that is horizontal to V4, and V6 is the liquid and center line that is horizontal to V4.

V1 and V2 mainly reflect the activity of the right ventricle, V3 and V4 have a high correlation with LEAD II, and V5 and V6 mainly reflect the activity of the left ventricle.

12 shows the electrocardiogram waveform output by the clinical electrocardiogram device. FIG. 13 illustrates the ECG waveform output when the sensing device is attached to the V1 position, and FIG. 14 illustrates the ECG waveform output when the sensing device is attached to the V2 position. FIG. 15 illustrates the ECG waveform output when the sensing device is attached to the V3 position, and FIG. 16 illustrates the ECG waveform output when the sensing device is attached to the V4 position. FIG. 17 illustrates the ECG waveform output when the sensing device is attached to the V5 position, and FIG. 18 illustrates the ECG waveform output when the sensing device is attached to the V6 position.

A pearson correlation coefficient graph calculated by comparing the electrocardiogram waveform measured at each position with the electrocardiogram waveform shown in FIG. 12 is shown in FIG. 19.

As shown in FIG. 19, it can be seen that the correlation between the data measured at the positions of V3 and V4 and the clinical electrocardiogram LEAD II is 80% or more. This is a comparison of the results obtained by measuring a plurality of subjects on average, and it is sufficiently predicted that a waveform having a higher correlation can be obtained when the measurement experiment is conducted on a larger sample group.

Although the above has been described with reference to embodiments of the present invention, those skilled in the art may variously modify the present invention without departing from the spirit and scope of the present invention as set forth in the claims below. And can be changed.

1 is a view showing a cardiac activity measuring method using the limb electrode induction method according to the prior art.

2 is a view showing a cardiac activity measuring method using a two-electrode method according to the prior art.

Figure 3 is a schematic diagram showing the configuration of a cardiac activity measurement system according to an embodiment of the present invention.

4 is a block diagram of a signal processor according to an exemplary embodiment of the present invention.

Figure 5 is a bottom view showing the shape of the electrode patch portion according to an embodiment of the present invention.

6 is a cross-sectional view illustrating a shape of a sensing device in which an electrode patch unit and a signal processing unit are coupled according to an embodiment of the present invention.

7 is a diagram illustrating a detailed configuration of a signal processing unit according to another embodiment of the present invention.

8 is a diagram showing the detailed configuration of a signal processing unit according to another embodiment of the present invention.

Figure 9 is a bottom view showing the shape of the electrode patch portion according to another embodiment of the present invention.

Figure 10 is a bottom view showing the shape of the electrode patch according to another embodiment of the present invention.

FIG. 11 is a schematic representation of the location of general chest leads (Precordial leads, Chest leads). FIG.

12 illustrates waveforms of a typical clinical electrocardiogram.

13 to 18 are diagrams showing the electrocardiogram waveform at each position when the sensing device is attached to each chest guide position according to an embodiment of the present invention.

Figure 19 is a comparison graph showing the correlation between the waveform and the clinical electrocardiogram at each chest induction position with a measuring device according to an embodiment of the present invention.

Claims (20)

Adhesive Three electrodes formed through the adhesive part and disposed at vertices of a triangle to detect a biopotential signal, and And an electrolyte region formed by applying an electrolyte to a peripheral region of each of the electrodes exposed on the bottom surface of the adhesive portion. The method of claim 1, Two of the three electrodes are used to receive a biopotential signal for differential amplification, and the other electrode is used as a reference electrode electrode patch. The method of claim 2, And the two electrodes for receiving a biopotential signal are arranged for LEAD II measurement. The method of claim 1, Electrode patch, characterized in that the medical adhesive is applied to the bottom of the adhesive portion. The method of claim 1, And the three electrolyte regions are spaced apart from each other. The method of claim 1, The adhesive patch, characterized in that one or more holes formed. The method of claim 6, The hole is an electrode patch, characterized in that used for sweat discharge or sensor exposure. Three electrodes are disposed through the adhesive part, and an electrode patch part is formed by applying an electrolyte to a peripheral area of each of the electrodes on a bottom surface of the adhesive part; And a signal processing unit coupled to the electrode patch unit to transmit a signal generated by amplifying a biopotential signal input through the electrode to a terminal device through a wireless communication method. The method of claim 8, The electrode patch unit and the signal processing unit is characterized in that coupled to the snap button (snap button) method. The method of claim 8, The electrode patch portion, Adhesive Three electrodes formed through the adhesive part and disposed at vertices of a triangle to detect a biopotential signal, and And an electrolyte region formed by applying an electrolyte to a peripheral region of each of the electrodes exposed on the bottom surface of the adhesive portion. The method of claim 8, The signal processing unit, An amplifier for amplifying a biopotential signal input through the electrode An A / D converter converting the amplified biopotential signal into a digital signal; And a communication performing unit converting the amplified digital signal into a wireless signal format and transmitting the converted digital signal to the terminal device in a wireless communication method. The method of claim 8, The signal processing unit, An amplifier for amplifying a biopotential signal input through the electrode Filtering unit for removing the noise component from the amplified biopotential signal An A / D converter converting the filtered biopotential signal into a digital signal A signal analyzer which analyzes the biopotential signal converted into a digital signal and extracts data on the electrical activity of the heart; And a communication performing unit converting the extracted data into a wireless signal format and transmitting the extracted data to the terminal device in a wireless communication method. The method of claim 10, And at least one hole is formed in the adhesive portion. The method of claim 13, The signal processing unit, A sensor unit comprising sensing means in contact with or in close proximity to the skin surface through the aperture An amplifier for amplifying a biopotential signal input through the electrode Filtering unit for removing the noise component from the amplified biopotential signal An A / D converter converting the filtered biopotential signal into a digital signal A signal analyzer for extracting data on electrical activity of the heart by analyzing the sensing signal sensed by the sensor unit and the biopotential signal converted into a digital signal; And a communication performing unit converting the extracted data into a wireless signal format and transmitting the extracted data to the terminal device in a wireless communication method. The method of claim 14, And a display unit which displays information on an operation state of the sensing device and at least one of the extracted data. The method of claim 14, The sensing device is a sensing device, characterized in that at least one of the body temperature sensor, the sound collection sensor. The method of claim 10, Two of the three electrodes are used to receive a biopotential signal to be differentially amplified, the other electrode is used as a reference electrode. The method of claim 10, And the two electrodes for receiving the biopotential signal are arranged for LEAD II measurement. The method of claim 10, Sensing device, characterized in that the medical adhesive is applied to the bottom of the adhesive portion. The method of claim 10, And the three electrolyte regions are spaced apart from each other.

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