KR102664086B1 - The electrode for measuring bio-signals - Google Patents

Abstract

It includes a circular electrode portion having a central hole into which a sensor for detecting biological signals is coupled and adhered to the skin, wherein the electrode portion is formed in a symmetrical shape with respect to the central hole so as to be divided into radial regions, or is formed of a plurality of An electrode for measuring biological signals is provided, wherein grooves are formed on one surface at equal intervals.

Description

The electrode for measuring bio-signals}

The present invention relates to an electrode for measuring biosignals, which has excellent adhesion and contact feeling according to the curved surface of the human body by modifying the area that touches the surface of the human body, and can also be applied to integrated smart clothing.

Due to the early entry into an aging society and the increase in chronic diseases such as high blood pressure, diabetes, and heart disease, Korea's medical expenses have increased the most among major OECD countries over the past 10 years. Increasing medical costs and interest in health are raising public interest in health care that can manage and prevent disease outbreaks. Therefore, wearable biosignal monitoring research is underway to monitor health in real time and respond quickly to emergency situations.

Currently, wearable bio-signal monitoring is being carried out through devices such as smart watches, smart belts, and smart clothing. In the case of smart clothing, bio-signal data can be measured mainly by connecting a sensor with electrodes to the clothing. Since biological signal measurement sensors are very important in measuring stable and accurate signals, various manufacturing methods for electrodes to which the measurement sensors are combined are being studied. The electrode refers to a device that is attached to the skin and monitors the potential difference in the body to transmit electrical signals inside the body to the outside. Currently, data can be obtained by detecting the potential difference of the transmitted signal, and this data can be used to analyze biosignals such as ECG (electrocardiogram) and EMG (electromyogram).

Until now, various types of electrodes, such as gel electrodes, metal electrodes, and fiber electrodes, have been used to measure biosignals. Gel electrodes, which are mainly used in medical institutions, are disposable, require frequent replacement, can cause environmental problems, and can cause side effects such as irritation and itching when used for a long time. Metal electrodes are not only hard and cold at the part that touches the skin, but also have low adhesion, making it difficult to obtain biosignals from body parts with high curvature.

Recently, much research has been conducted to develop textile electrodes that do not cause discomfort when contacted with the skin and are easy to attach to clothing. When wearing smart clothing equipped with fiber electrodes, accurate and stable biosignals can be obtained in an upright position, but during free activity, the fiber electrodes may come off the body, generate noise, and lead to inaccurate measurement results. Additionally, when applied to smart clothing, the wearer may feel uncomfortable due to contact with the sensor. Therefore, there is a need to develop electrodes for measuring biosignals that can not only measure stable and accurate data but also improve wearing comfort. To this end, research on materials and designs related to electrode contact with the body, research on the design of electrodes in contact with the body, and research on the optimal location of electrodes are being conducted in the fashion industry. According to previous research results, the design, structure, and attachment location of electrodes are important to obtain high-quality signals, but there is a lack of research on modifying the electrode structure and applying it to smart clothing. In particular, 3D printing is applied to develop electrodes with high adhesion to the body. It can be seen that research to develop the shape is necessary.

Korean Patent No. 10-1527937 (registration date: June 4, 2015) Korean Patent No. 10-1538426 (registration date: July 15, 2015) Korean Patent Publication No. 10-2021-0016760 (Publication Date: February 17, 2021)

The technical problem to be achieved by the present invention is to provide an electrode for measuring bio-signals that can improve adhesion and comfort upon contact for accurate measurement of bio-signals and can be applied to smart clothing.

The purpose of the present invention is not limited to the purposes mentioned above, and other purposes not mentioned will be clearly understood by those skilled in the art from the description below.

In order to solve the above problem, the present invention includes a circular electrode unit that is attached to the skin and has a central hole into which a sensor for detecting biological signals is coupled, and the electrode unit is based on the central hole so that the area is divided radially. An electrode for measuring biosignals can be provided, which is formed in a symmetrical shape or has a plurality of grooves formed on one surface at equal intervals.

The electrode unit includes a first structure in which a plurality of holes are arranged radially linearly, a second structure including a region cut out to be divided into a fan shape, a third structure in which a grid-shaped groove is formed on one surface, and a plurality of stripes. The groove may be formed by a selected one of the fourth structures formed on one surface.

The first structure may have a plurality of holes arranged at equal intervals so as to be radially linear in eight directions from the center.

The first structure may be one in which a plurality of holes are formed with a diameter that is 0.04 to 0.06 of the diameter of the electrode part, and each hole is arranged at an interval corresponding to the diameter of the hole.

The second structure may have eight regions divided into the fan shape.

The second structure is cut from a point 0.04 to 0.06 of the diameter of the electrode from the center hole to the outer periphery of the electrode, and the width of the outer periphery of the electrode to be cut is 0.04 to 0.06 of the diameter of the electrode. It may be.

The third or fourth structure may have a plurality of grooves formed in a grid or stripe shape at intervals of 0.1 to 0.15 of the electrode portion diameter.

The third or fourth structure may have a plurality of grooves formed in a grid or stripe shape with a line width of 0.02 to 0.03 of the electrode diameter and a depth of 0.006 to 0.013.

The electrode unit may include a conductive material or a thermoplastic polyurethane material.

The electrode portion may be formed by 3D printing.

The electrode for measuring biological signals according to an embodiment of the present invention is formed in a symmetrical shape with respect to a central hole so that the area is divided radially, or has an electrode portion in which a plurality of grooves are formed on one side at equal intervals, thereby accurately measuring biological signals. It can improve adhesion and comfort upon contact for measurement, and has the advantage of being applicable to smart clothing.

1 is a perspective view and cross-sectional view showing a disc-shaped electrode for measuring biological signals;
Figure 2 is a perspective view showing an electrode for measuring biosignals according to a first embodiment of the present invention;
Figure 3 is a perspective view showing an electrode for measuring biological signals according to a second embodiment of the present invention;
Figure 4 is a perspective view showing an electrode for measuring biological signals according to a third embodiment of the present invention;
Figure 5 is a perspective view showing an electrode for measuring biological signals according to a fourth embodiment of the present invention;
Figures 6 and 7 are images of the skin contact surface of the brachioradialis muscle using electrodes for measuring biosignals according to embodiments of the present invention;
Figures 8 and 9 are images of the skin contact surface of the rectus femoris muscle using electrodes for measuring biological signals according to embodiments of the present invention.

Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the attached drawings. The embodiments introduced below are provided as examples so that the idea of the present invention can be sufficiently conveyed to those skilled in the art. Accordingly, the present invention is not limited to the embodiments described below and may be embodied in other forms. Also, in the drawings, the length and thickness of layers and regions may be exaggerated for convenience. Like reference numerals refer to like elements throughout the specification.

Figure 1 is a perspective view and a cross-sectional view showing a disk-shaped electrode for measuring bio-signals, Figure 2 is a perspective view showing an electrode for measuring bio-signals according to a first embodiment of the present invention, and Figure 3 is a second embodiment of the present invention. Figure 4 is a perspective view showing an electrode for measuring biological signals according to a third embodiment of the present invention, and Figure 5 is a perspective view showing an electrode for measuring biological signals according to a fourth embodiment of the present invention. It is a perspective view showing the electrode, and Figures 6 and 7 are images of the skin contact surface of the brachioradialis muscle using electrodes for measuring biosignals according to embodiments of the present invention, and Figures 8 and 9 are embodiments of the present invention. This is an image of the skin-contact surface of the rectus femoris muscle using electrodes for measuring biosignals.

Referring to Figures 1 to 9, the electrode 10 for measuring bio-signals according to an embodiment of the present invention has a central hole 101 into which a sensor for detecting bio-signals is coupled, and has a circular electrode portion attached to the skin. It includes (100), and the electrode unit 100 may be formed in a symmetrical shape with respect to the central hole 101 so that the area is divided radially, or a plurality of grooves may be formed on one surface at equal intervals. there is. Therefore, the electrode unit 100 is formed in a symmetrical shape with respect to the central hole 101 so as to be divided into radial regions, or has a plurality of grooves formed on one surface at equal intervals to ensure adhesion for accurate measurement of biological signals. It can improve comfort when in contact with and has the advantage of being applicable to smart clothing.

In detail, the bio-signal measuring electrode 10 has a central hole 101 into which a sensor for detecting bio-signals is coupled and may include a circular electrode portion 100 that is adhered to the skin and is in contact with the skin. It may include a gel pad 200 attached to one surface. The electrode portion 100 may have a thickness (B) that is 0.012 to 0.025 times the diameter of the electrode portion (A). In order to reduce the flexural modulus of elasticity and thereby increase flexibility, the electrode portion diameter ( The thickness (B) may be 0.012 to 0.013 times that of A). A lower flexural modulus of elasticity means more flexibility, and as flexibility increases, adhesion can be further improved. For example, the electrode unit 100 with a diameter of 40 mm may have a thickness of 0.4 to 1.2 mm, and preferably may have a thickness of 0.4 to 0.6 mm. In addition, in the above case, the gel pad 200 is conventional and can be provided in various shapes and sizes, and has a thickness of 0.8 to 1.2 mm so that the influence on the flexural modulus of elasticity of the electrode unit 100 is minimized. You can.

The electrode unit 100 may include a conductive material or a thermoplastic polyurethane material.

Furthermore, the electrode unit 100 may be formed by 3D printing. Therefore, the electrode 10 for measuring biological signals can be manufactured by directly printing a conductive material or thermoplastic polyurethane material on fabric, and there is an advantage in easily manufacturing smart wear. As an example, the electrode unit 100 can be formed using a 3D printer of the FDM (Fused Deposition Modeling) method using a filament made of thermoplastic polyurethane (TPU: Thermoplastic Polyurethane).

The electrode unit 100 includes a first structure 120 in which a plurality of holes 122 are arranged radially linearly, a second structure 130 including a region 133 cut to be divided into a fan shape, and a grid. It may be formed as a selected one of the third structure 140 in which grooves 144 of the shape are formed on one side, and the fourth structure 150 in which a plurality of stripe-shaped grooves 155 are formed on one side. Due to the first to fourth structures described above, the electrode unit 100 can change the bending elastic modulus, thereby securing flexibility and adhesion to different bends for each part of the human body. In addition, when forming the electrode unit 100 on smart wear using 3D printing, electrodes with different structures that ensure adhesion can be formed for each part of the human body with different curves, thereby further improving adhesion to the skin. It is possible to manufacture smart wear that improves the accuracy of biosignal measurement.

For example, the first structure 120 as shown in FIG. 2 may have a plurality of holes 122 arranged at equal intervals so as to be radially linear in eight directions from the center. As a result, the electrode portion 100 can be divided into eight radial regions and have a symmetrical shape with respect to the central hole 101.

In the first structure 120, a plurality of holes 122 are formed with a diameter 122a that is 0.04 to 0.06 of the electrode portion diameter A, and each hole 122 has a diameter 122a of the hole. It may be arranged at intervals 122b corresponding to . In this case, the first hole may be located at a point 122c that is 0.04 to 0.06 of the electrode diameter A from the center hole 101.

The second structure 130 as shown in FIG. 3 may have eight regions divided into a fan shape. That is, the radially formed incision area 133 divides the electrode unit 100 into eight fan-shaped areas, so that the electrode unit 100 having a symmetrical shape with respect to the central hole 101 can be provided.

The second structure 130 is cut from the center hole 101 to the outer periphery of the electrode portion from a point 133c that is 0.04 to 0.06 of the electrode diameter A. The width of the outer periphery of the electrode portion is cut. (133a) may have a size of 0.04 to 0.06 of the electrode diameter (A).

As shown in Figure 4 or Figure 5, the third structure 140 or the fourth structure 150 is in a grid shape 144 or stripes with intervals 144c and 155c having a size of 0.1 to 0.15 of the electrode diameter A. A plurality of grooves may be formed in the mold 155. That is, by providing the third structure 140 or the fourth structure 150, the electrode portion 100 in which a plurality of grooves 144 and 155 are formed on one surface at equal intervals can be provided.

In this case, the third structure 140 or the fourth structure 150 has line widths 144a and 155a having a size of 0.02 to 0.03 of the electrode portion diameter (A) and a depth ( A plurality of grooves may be formed in a grid shape (144) or a stripe shape (155) (144b, 155b). In addition, the plurality of grooves have a line width (144a, 155a) having a size of 0.02 to 0.03 of the electrode portion diameter (A) and a depth (144b, 155b) having a size of 0.4 to 0.6 of the electrode portion thickness (B). ) may be formed in a grid shape (144) or a stripe shape (155). Furthermore, the plurality of grooves formed on one surface may be formed on the lower surface in close contact with the skin or on the upper surface exposed to the outside when mounted on smart clothing or attached to the skin. To further improve adhesion to the skin, the plurality of grooves may be formed on the upper surface. It is desirable to form

Hereinafter, the electrode for measuring biological signals according to the present invention will be described through the following experimental examples. The following experimental examples are only examples for explaining the present invention, and the present invention is not limited thereto.

Manufacture of electrodes for measuring biological signals

For a comparative example, a plain electrode was formed in a circle with a diameter of 40 mm and a center hole with a diameter of 4 mm was formed. A first structure was formed in which four holes with a diameter of 2 mm were formed at 2 mm intervals to be arranged radially linearly every 45 degrees. A first electrode having a fan-shaped cut area from a point 2 mm away from the center hole at 45ㅀ intervals, a second electrode having a second structure (radial cut-out) with a width cut from the circumference of 2 mm, A third electrode having a third structure (Check) in which a central hole is formed and grooves with a horizontal and vertical width of 1 mm are formed at 5 mm intervals, and a fourth structure (Stripe) in which a central hole is formed and grooves with a horizontal width of 1 mm are formed at 5 mm intervals. ) was formed to have a fourth electrode. In addition, each electrode was manufactured in two cases, with a thickness of 1 mm and 0.5 mm. For the electrode with a thickness of 1 mm, the depth of the grooves of the third and fourth structures was 0.5 mm, and for the electrode with a thickness of 0.5 mm, the depth of the grooves of the third and fourth structures was 0.5 mm. In this case, the depth of the grooves of the third and fourth structures was formed to be 0.25 mm. Each of the 10 electrodes was modeled using the Geomagic Design An FDM-type 3D printer was used, and the printing conditions were set to 100% internal density, discharge temperature setting of 230℃, bed temperature of 65℃, and printing speed of 15~30mm/s.

Flexural modulus test of electrodes for measuring biological signals

The experiment was conducted in accordance with ASTM D 790-99, the test standard for curvature evaluation of non-reinforced materials and plastics, and specimens were produced for this purpose. For each thickness of 1mm and 0.5mm, the specimen size of the disk-shaped electrode and the first to fourth electrodes was 127ㅧ12.7ㅧ5mm, 127ㅧ12.7ㅧ10mm, the span length was 80mm, and the descending speed of the crosshead was evaluated at 3 points bending. It was 2.1mm/min.

Adhesion test of electrodes for measuring biological signals

A 1 mm thick gal pad was attached to 10 samples of disk-shaped electrodes, first to fourth electrodes, manufactured with thicknesses of 1 mm and 0.5 mm, and then attached to the brachioradialis muscle (arm) and rectus femoris muscle (thigh). The contact area was photographed using a thermal imaging camera (Flir One Pro) for 5 minutes, and 5 images were acquired at 1-minute intervals. The contact area of each image was measured, and the ratio compared to the non-contact area was calculated. The radius of curvature of the brachioradialis muscle is 3.36 cm horizontally and 15.55 cm vertically, and the radius of curvature of the rectus femoris muscle is 4.96 cm horizontally and 43.29 cm vertically, and the radius of curvature of the brachioradialis muscle is larger than that of the rectus femoris muscle.

Test of contact sensation of electrodes for measuring biological signals

Twenty-year-old healthy adults in their 20s (10 men, 10 women) with no brain or cognitive disease or history were selected as subjects, and the experimental procedure was approved by the IRB (Institutional Review Board) (No. 202106- HR-013-01). All participants received sufficient sleep the day before the experiment, and were prohibited from alcohol, caffeine, drugs, excessive exercise, and napping for 12 hours before the experiment as they may affect the nervous system. If a participant's health or fatigue was abnormal on the day of the experiment, they were excluded from the experiment to minimize the impact of physical conditions related to concentration. The human body characteristics of the participants are shown in <Table 1>.

Participant Age (years) Height (cm) Weight (kg) other Mean(SD) 21.80(1.01) 176.60(4.12) 70.23(6.28) female Mean(SD) 21.50(0.98) 162.25(3.97) 52.05(5.82)

Using BioBrain Inc. (Daejeon), electroencephalogram (EEG) was recorded according to attachment for each of 10 types of electrodes. Electroencephalography (EEG) is performed according to the International 10-20 System: F3 (left hemisphere, frontal lobe), F4 (right hemisphere, frontal lobe), T3 (left hemisphere, temporal lobe), T4 (right hemisphere, temporal lobe), O1 (left hemisphere, occipital lobe), O2 ( Measurements were made at seven locations: right hemisphere, occipital lobe) and Cz (crown). The reference electrode of A1 was attached behind the left earlobe, and the ground electrode was attached to the forehead. EEG signals were digitized at a sampling frequency of 250 events per second (250 Hz). EGG analysis indicators and frequency range are shown in Table 2.

abbreviation full term frequency range RT Relative theta power spectrum (4∼8Hz) / (4∼50Hz) R.A. Relative alpha power spectrum (8∼13Hz) / (4∼50Hz) RB Relative Beta Power Spectrum (13∼30Hz) / (4∼50Hz) RG Relative gamma power spectrum (30∼50Hz) / (4∼50Hz) R.F.A. Relatively fast alpha power spectrum (11∼13Hz) / (4∼50Hz) RSA Relative slow alpha power spectrum (8∼11Hz) / (4∼50Hz) RLB Relatively low beta power spectrum (12∼15Hz) / (4∼50Hz) RMB Relative mid-beta power spectrum (15∼20Hz) / (4∼50Hz) RHB Relatively high beta power spectrum (20∼30Hz) / (4∼50Hz) RST SMR to theta ratio (12∼15Hz) / (4∼8Hz) RMT Mid Beta to Theta Ratio (15∼20Hz) / (4∼8Hz) RSMT Ratio of SMR~Mid Beta) to Theta (12∼20Hz) / (4∼8Hz) RAHB Alpha to High Beta Ratio (8∼13Hz) / (20∼30Hz)

To reduce individual differences in EEG analysis indices, basic EEG values were subtracted from the experimental EEG and 91 values (7 measurement locations * 13 analysis indices) were analyzed. EEG measurements according to the type of electrode sensor were conducted in a laboratory with a room temperature of 23ㅁ2℃ and a relative humidity of 50ㅁ5%. Participants wore a special fabric cap with EEG electrodes attached (BIOS_Dry_8, Biobrain), measured basal EEG for 1 minute in a relaxed state, attached experimental electrodes to the forearm, and measured EEG for 1 minute. Only data excluding the 10 seconds from the start of measurement and the 10 seconds from the end of measurement were used. After measuring the EEG, subjective evaluations were made on four items: 'skin adhesion', 'touch', 'flexibility', and 'overall comfort', and a 1-minute break was given. The subjective evaluation was made using a 7-point Likert scale, ranging from 1 for ‘strongly disagree’ to 7 for ‘strongly agree.’ Electrodes were presented to participants using a modified Latin square design to minimize order effects, and all measured data were statistically processed using SPSS 26.0 (IBM, New York, USA). T-test of individual samples was used to analyze differences in EEG index according to gender, and ANOVA and Duncan's post hoc test were performed to analyze differences in EEG index according to electrode type. Significance was set at p <.05.

Result 1- Flexural modulus

Flexural modulus refers to stiffness or softness, and can be considered an important factor in evaluating not only flexibility but also adhesion to the skin. The measurement results of the flexural modulus of elasticity for 10 electrodes are shown in Table 3.

Electrode thickness
Electrode type 5mm 10mm Comparative example Disk-shaped structure (Plain) 53.6 78.8 Experiment example First structure (Circular) 46.3 94.2 Second structure (radial cut-out) 34.2 47.0 Third Structure (Check) 10.7 15.8 Fourth Structure (Stripe) 10.5 12.0

The flexural elastic modulus varies depending on the thickness and shape. For the electrode with a thickness of 5 mm, the disc-shaped structure, which is a comparative example, showed the highest flexural elastic modulus, and for the electrode with a thickness of 10 mm, the first structure (Circular) showed the highest flexural elastic modulus. showed. The lower the bending elastic modulus, the more flexible it is, and the third structure (Check) and fourth structure (Stripe) are the most flexible in both thicknesses. In addition, it can be seen that in all types of electrodes, the flexural elastic modulus is greater at a thickness of 10 mm than at 5 mm, and flexibility decreases as the thickness increases.

Result 2 - Adhesion of electrodes for measuring biosignals

Figures 6 and 7 are images of the skin contact surface of the brachioradialis muscle using electrodes for measuring bio-signals according to embodiments of the present invention, and Figures 8 and 9 are images of bio-signal measurement according to embodiments of the present invention. These are images of the skin-contact surface of the rectus femoris muscle using an electrode. Figures 6 and 8 show an electrode thickness of 1 mm, and Figures 7 and 9 show an electrode thickness of 0.5 mm.

The brighter the color of the electrode, the higher the adhesion to the skin. As a result of analyzing the adhesion of each electrode through video, it can be seen that the adhesion of the rectus femoris muscle (thigh) is higher. For both the rectus femoris and brachioradialis muscles, skin adhesion was higher when the thickness was 0.5 mm, and for the brachioradialis muscle, when the thickness was 1 mm, the adhesion strength of the second structure (radial cut-out) was higher, and when the thickness was 0.5 mm, the adhesion strength of the third structure (radial cut-out) was higher. Check) and the fourth structure (Stripe) had better skin adhesion.

The separation rate from the skin for each electrode is shown in Table 4 below. When looking at the separation rate of the electrodes, the adhesion in the arm area where the radius of curvature in the horizontal direction of the human body is 3.36 is excellent for the second structure (radial cut-out) when the electrode thickness is 1 mm, and when the electrode thickness is 0.5 mm, the adhesion is excellent. In this case, it can be seen that the third structure (Check) and fourth structure (Stripe) are excellent. In the thigh area where the radius of curvature in the horizontal direction is 4.96, the adhesion of the third structure (Check) is excellent when the electrode thickness is 1 mm, and the adhesion of the electrode with a thickness of 0.5 mm is excellent in all designs.

measuring area Thickness (mm) Electrode type Separation rate (%) brachioradialis muscle 1.0 First structure (Circular) 8.6~28.4 Second structure (radial cut-out) 2.2~16.0 Third Structure (Check) 10.4~35.7 Fourth Structure (Stripe) 10.8~32.1 0.5 First structure (Circular) 2.3~17.7 Second structure (radial cut-out) 1.3~13.7 Third Structure (Check) 0 Fourth Structure (Stripe) 0 rectus femoris 1.0 First structure (Circular) 8.2~32.7 Second structure (radial cut-out) 0~15.4 Third Structure (Check) 0~4.0 Fourth Structure (Stripe) 0~29.3 0.5 First structure (Circular) 0 Second structure (radial cut-out) 0 Third Structure (Check) 0 Fourth Structure (Stripe) 0

Result 3 - Contact sensation of electrodes for measuring biosignals

The feeling of contact of the electrode was subjectively evaluated and measured on a 7-point Likert scale in response to 4 questions regarding skin adhesion, contact feeling, flexibility, and overall comfort.

When examining brain wave changes according to gender, significant differences were found in 'RA', 'RFA', 'RSA', 'RG', 'RST', 'RMT', and 'RSMT' indicators. In men, the 'RG' indicator, which indicates high level of cognition, anxiety, stress, and arousal, and the 'RST', 'RMT', and 'RSMT' indicators, which indicate concentration, were highly activated, while in women, the 'RG' indicator, which indicates stability and rest, was highly activated. The 'RA' indicator, the 'RFA' indicator, which means calm and semi-concentrated, and the 'RSA' indicator, which means relaxation and rest, were highly activated. Therefore, even if electrodes for measuring biosignals for men and women have the same structure, the perceived brain waves are different depending on gender, so it can be expected that it will be more efficient if the design concept is different according to gender when developing electrodes.

As a result of examining EEG changes according to electrode type by gender, no significant differences occurred in men, but in women, significant differences in the 'RA' index were seen depending on the type of electrode in the right temporal lobe (T4). When equipped with this third structure, the RA' indicator was highly activated compared to other structures. However, no significant difference was found depending on the thickness of the electrode. Therefore, the electrode on which the third structure (Check) is formed can be judged to have a good sense of touch. In the case of the third structure (Check), compared to other structures, it could be bent in various directions up, down, left, and right due to the lattice grooves, so it could be easily deformed according to the curvature of the human body, and the flexural elastic modulus measurement result was also small, which was due to the electrode This means that the flexibility is great and the contact feeling is also excellent. As a result of subjective evaluation according to the type of electrode, significant differences were found in all items, and overall, the third structure (Check) and fourth structure (Stripe) were preferred for the electrode type and the thickness of 0.5 mm.

The electrode 10 for measuring biological signals according to an embodiment of the present invention is formed in a symmetrical shape with respect to a central hole so that the area is divided radially, or the electrode portion 100 has a plurality of grooves formed on one side at equal intervals. By providing a , it is possible to improve adhesion and comfort upon contact for accurate measurement of biological signals, and has the advantage of being applicable to smart clothing.

Although the present invention has been described above with reference to preferred embodiments, those skilled in the art may make various modifications and changes to the present invention without departing from the spirit and scope of the present invention as set forth in the claims below. You will understand that you can do it.

10; Electrodes for measuring biosignals
100; electrode part
101; central hall
110; disc-shaped structure
120; first structure
122; hall
130; second structure
133; incision area
140; 3rd structure
144; grid groove
150; 4th structure
155; Striped groove
200; gel pad

Claims (10)

It has a central hole into which a sensor that detects biological signals is coupled, and includes a circular electrode portion that is adhered to the skin,
The electrode part,
It has a thickness of 0.012 to 0.025 times the diameter of the electrode part,
in a symmetrical shape with respect to the central hole so that the area is divided radially.
An electrode for measuring biosignals, characterized in that it is formed by a selected one of a first structure in which a plurality of holes are arranged radially linearly, and a second structure including an area cut out to be divided into a fan shape. delete According to paragraph 1,
The first structure is an electrode for measuring biological signals, characterized in that a plurality of holes are arranged at equal intervals so as to be radially linear in eight directions from the center. According to paragraph 1,
The first structure is an electrode for measuring biological signals, wherein a plurality of holes are formed with a diameter that is 0.04 to 0.06 of the diameter of the electrode part, and each hole is arranged at an interval corresponding to the diameter of the hole. According to paragraph 1,
The second structure is an electrode for measuring biosignals, characterized in that there are eight regions divided into the fan shape. According to paragraph 1,
The second structure is cut from a point 0.04 to 0.06 of the diameter of the electrode from the center hole to the outer periphery of the electrode, and the width of the outer periphery of the electrode to be cut is 0.04 to 0.06 of the diameter of the electrode. An electrode for measuring biosignals, characterized in that. It has a central hole into which a sensor that detects biological signals is coupled, and includes a circular electrode portion that is adhered to the skin,
The electrode part,
It has a thickness of 0.012 to 0.025 times the diameter of the electrode part,
The third structure or the fourth structure is selected from the group consisting of a third structure in which a plurality of grooves are formed on one surface at equal intervals to form a grid-shaped groove on one surface, and a fourth structure in which a plurality of stripe-shaped grooves are formed on one surface. An electrode for measuring biosignals, characterized in that a plurality of grooves are formed in a grid or stripe shape at intervals of 0.1 to 0.15 of the electrode diameter. In clause 7,
The third or fourth structure is a living body characterized in that a plurality of grooves are formed in a grid or stripe shape with a line width of 0.02 to 0.03 of the electrode diameter and a depth of 0.006 to 0.013. Electrodes for signal measurement. According to claim 1 or 7,
An electrode for measuring biological signals, wherein the electrode unit includes a conductive material or a thermoplastic polyurethane material. According to claim 1 or 7,
An electrode for measuring biosignals, wherein the electrode part is formed by 3D printing.