KR20200061584A - Dray adhesive skin patch - Google Patents

Abstract

The present invention relates to a bio-adhesive sensor. The bio-adhesive sensor of the present invention does not use a separate adhesive unlike the conventional sensor. The excellent adhesion due to a structure of an adhesive part is exhibited so that the adhesion to the skin is excellent, the repeated use is possible, and the irritation to a surface to be bonded can be minimized.

Description

Dry adhesive skin patch {DRAY ADHESIVE SKIN PATCH}

The present invention relates to an adhesive electrode for measuring a biosignal, and in a wet environment, for example, on a surface of a skin in motion, without a chemical adhesive, while maintaining the adhesiveness, and relates to an adhesive electrode capable of high sensing of a biosignal. .

Wearable devices (wearable devices) are related to computers and clothing and accessories that incorporate conventional electronic technology, and such wearable devices often interact in direct contact with the human body, and thus various sciences on the interface between the device and the human body are developed and have. Recently, according to this trend, demand and research for a diagnostic wearable device fused with a diagnostic device are steadily increasing, taking advantage of the dry adhesive technology. For example, researchers have tried to apply dry adhesive technology to improve the stability, breathability, and further amplify the biosignal, which was lacking in manufacturing patch-type sensors that measure biosignals such as electrocardiograms and pulses or cosmetic patches for cosmetic purposes. It continues.

There are various mechanisms of adhesion in nature, such as snail mucus, mussel protein, insect wing splicing, gecko lizard feet, cockle spider feet, and thistle seeds. These natural adhesive systems are very efficient, and many types of adhesives such as medical bands, adhesive tapes, post-it, and Velcro have been developed by imitating them. However, in order to fasten the patch-type ultra-high sensitivity sensor to the target, an adhesive method meeting the following conditions must be used. First of all, a large disturbance (noise) should not occur in the signal transmission process due to the adhesion site. Next, it should have sufficient adhesive strength regardless of the curvature or roughness of the surface to be measured so that the patch does not easily fall off. In addition, it is easy to attach and detach, and adhesive strength must be maintained in the process. Finally, the surface of the object to be measured should not be damaged, and in particular when it is adhered to human skin, an adhesive method that does not cause skin irritation, contamination, or discomfort should be used.

Therefore, there is a limitation in the use of the wet type adhesive method, which has problems such as requiring a high strength for desorption, leaving traces after desorption, skin trouble, and deteriorating adhesive strength when repeatedly used. In this context, biomimetic-based dry adhesive systems have been studied in various fields as the concept of dry adhesives that can be repeatedly detached by the interaction of micro cilia and do not leave any contamination and damage on the surface, but still use the existing medical wet tape. It has not reached the replacement level of adhesion. In addition, in the case of a wearable sensor for skin adhesion, various technical concepts have been reported, but the problem of breathability or bonding between the device and the skin interface has not been sufficiently studied.

An object of the present invention is to provide an adhesive electrode capable of high sensing of a biosignal while maintaining adhesion without a chemical adhesive, in a humid environment, for example, on the surface of a skin in motion.

In one aspect, the present invention is composed of an elastic polymer containing a conductive material, and includes a plurality of microstructures on a part of the surface, the microstructures characterized in that the sucker chamber of the intaglio shape dug from the surface, biosignal measurement Alternatively, a dry, sticky skin patch is provided for sensing.

The dry adhesive skin patch, the elastic polymer itself contains a conductive material and has the ability to transmit electricity, it is possible to measure the electrical signal by itself, or physical changes occurring from the living body, such as pulse, movement of the resistance value In particular, the patch of the present invention may include a special microstructure on the surface, and can be stably attached to a wet surface, such as sweaty skin, without a separate chemical adhesive. It can be used as an electrode for measuring a high bio-signal in a humid environment or a sensor capable of sensing a physical signal of a bio-material.

The conductive material is characterized in that it includes at least one of carbon black, carbon nano tube (CNT), graphene flake graphite, and graphene. .

The elastic polymer is natural rubber, nitrile rubber, acrylonitrile-butadiene rubber, styrenebutadienerubber, chloroprene rubber, butyl rubber , Isoprene isobutylene rubber (isoprene-isobutylene rubber), ethylene propylene rubber, chlorosulphonated polyethylene rubber, chlorosulphonated polyethylene rubber, acrylic rubber, fluoro rubber, polysulfide Polysulfide rubber, silicone rubber, butadiene rubber, isoprene rubber, urethane rubber, polyurethane, polydimethylsiloxane (PDMS), polyolefin thermoplastic elastomer ( polyolefin thermoplastic elastomer, TPE, polystyrene TPE, polyvinyl chloride TPE, polyester TPE, polyurethane TPE, polyamide TPE, and these It characterized in that it comprises at least one of the mixture of.

It characterized in that it includes a hill-shaped embossed portion on the base surface of the sucker, the height of the hill-shaped embossed portion is smaller than the depth of the sucker chamber.

The shape of the hill-shaped embossed portion is characterized in that the circumference of the middle portion of the trunk is larger than the circumference of the top and bottom.

The microstructure is cylindrical, and the hill-shaped embossed portion is characterized in that it has a spherical or hemispherical shape protruding from the base surface.

The diameter of the cylinder is 1㎛ to 100㎛, characterized in that the height of the cylinder is 1㎛ to 100㎛, its aspect ratio is characterized in that 2/3 to 3.

The arrangement spacing of the plurality of microstructures is characterized in that it is 1:1 to 1:3 with respect to the diameter of the sucker.

The size of the circumference of the hill-shaped embossed portion is smaller than the circumference of the sucker chamber, and the longest circumferential surface of the hill-shaped embossed portion is attached to the surface to be adhered to without being pressed against the back surface of the electrode for adsorption to the sucker chamber. It is characterized in that it does not contact the periphery of the sucker chamber, and when the back side of the electrode is pressed, the longest circumferential surface is configured to adhere to the inner surface of the sucker chamber.

The bio-adhesive electrode is also attached to the surface to be adhered having a humid environment, and is characterized in that it senses the amplified bio-signal compared to the case where there is no microstructure of the embossed or intaglio sucker chamber.

In particular, the present invention claims that it can be used as a sensor or as an electrode depending on the concentration of carbon black in the elastomer.

When the concentration of carbon black in the elastic polymer is 4.0 vol% or less, preferably 4.0 vol% or less, the physical value of the patch, for example, the value of resistance according to elongation is greatly changed and can be used as a sensor for a physical signal of a living body. In particular, the dry-adhesive skin patch of the present invention maintains adhesion in skin having a humid environment, and provides an amplified sensing rate than when the microstructure is not present.

When the concentration of carbon black in the elastic polymer is 4.0 vol% or more, preferably 7.0 vol% or more, the physical change of the patch, for example, the resistance value according to the elongation is hardly changed, and adhesion is maintained even in a humid environment, and electrical signal measurement It can be used as an electrode for measuring bio signals, where the rate is not reduced.

The patch of the present invention may be an electrode for health monitoring.

The patch of the present invention may be an electrode for ECG (electrocardiogram).

The present invention provides a sensor for sensing a biosignal, including the patch of the present invention.

The bio-adhesive electrode according to the present invention is composed of a composite containing an elastic polymer and a conductive material, and is elastic and has excellent conductivity. Therefore, it can be variously applied as an elastic electrode, and the electrode includes a microstructure having a sucker chamber, so that adhesion is possible without using a separate adhesive, and manufacturing of a large area is easy. Accordingly, it is possible to minimize contamination, irritation, etc. on the surface to be adhered, for example, on the surface of the skin, regardless of the humidity of the surface to be adhered, for example, it exhibits excellent adhesion even in a humid environment and in an extended state. It is possible. When the elastic bio-adhesive electrode of the present invention is used in combination with a sensor, various changes of the surface to be adhered can be sensitively and quickly detected. As a result, it is possible to measure a biosignal that was difficult to measure using only the conventional sensor technology by using the bioadhesive patch and the wearable device according to the present invention, and to improve the diagnostic accuracy of physical diseases of the body.

1 is a schematic view showing a bio-adhesive electrode according to an embodiment of the present invention.
2 is a view showing a pattern mold manufacturing method of the present invention according to an embodiment.
3 is a view showing a method of manufacturing a bio-adhesive sensor of the present invention according to an embodiment.
4 is a view showing the results of the adhesion test of the bio-adhesive electrode according to an embodiment of the present invention.
5 is a view showing the electrical property test results of the bio-adhesive electrode according to an embodiment of the present invention.
6 is a view showing the results of a bio-sensing experiment of a bio-adhesive electrode according to an embodiment of the present invention.

The terms used in the present application are only used to describe specific embodiments and are not intended to limit the present invention. Singular expressions include plural expressions unless the context clearly indicates otherwise. In this application, the terms "include" or "have" are intended to indicate the presence of features, steps, actions, components, parts or combinations thereof described in the specification, one or more other features or steps. It should be understood that it does not preclude the existence or addition possibility of the operation, components, parts or combinations thereof.

Unless defined otherwise, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by a person skilled in the art to which the present invention pertains. Terms such as those defined in a commonly used dictionary should be interpreted as having meanings consistent with meanings in the context of related technologies, and should not be interpreted as ideal or excessively formal meanings unless explicitly defined in the present application. Does not.

The bio-adhesive electrode of the present invention is an elastic polymer composite electrode containing a conductive material, the electrode includes a plurality of microstructures on a part of the surface of the electrode, and the microstructure is an intaglio structure excavated on a part of the surface of the electrode, The intaglio structure includes a sucker chamber, and the electrode is used for sensing electrical signals in a living body.

In one embodiment, the electrode may further include at least one of an ultraviolet curable polymer and a heat curable polymer.

In one embodiment, the conductive material is at least one of carbon black, carbon nano tube (CNT), graphene flake graphite, graphene, and mixtures thereof. It may be including the above.

In one embodiment, the electrode may have a conductive material concentration of 10.0 vol% or less. For example, the electrode may have a carbon black concentration of 10.0 vol% or less. For example, it may be 1.0 vol% to 10.0 vol%. For example, when the concentration of carbon black in the electrode is 7.0 vol% or more, the proportion of carbon black, which is a conductive material, increases, and thus the proportion of the elastic polymer decreases, making it impossible to manufacture in the form of a patch, and the sensing sensitivity of the electrode decreases. Problems may occur, and if it is 1.0 vol% or less, there may be difficulty in using it as an electrode because the conductive material is too small, the conductivity is low and the electricity does not pass.

Although not limited thereto, in one embodiment, the conductive material may be in the form of particles, may be in the form of nanowires, nanofibers, and may include metal particles.

In one embodiment, the elastic polymer is natural rubber, natural nitrile rubber, nitrile rubber, acrylonitrile-butadiene rubber, styrenebutadienerubber, chloroprene rubber, butyl rubber (butyl rubber), isoprene isobutylene rubber, ethylene propylene rubber, chlorosulphonated polyethylene rubber, acrylic rubber, fluoro rubber ), polysulfide rubber, silicone rubber, butadiene rubber, isoprene rubber, urethane rubber, polyurethane, polydimethylsiloxane (PDMS), poly Polyurethane Acrylate, Polyolefin Thermoplastic Elastomer (TPE), Polystyrene TPE (Polystyrene TPE), Polyvinyl Chloride TPE (Polyvinyl Chloride TPE), Polyester TPE (Polyester TPE), Polyurethane TPE polyurethane TPE) polyamide TPE (polyamide TPE) and mixtures thereof.

In one embodiment, when the electrode contains a bio-friendly polymer such as polyurethane acrylate and PDMS, the adhesive strength is not significantly reduced, durability is maintained, and applied to the skin even if the electrode is repeatedly detached and attached to the skin several times. Irritation and contamination can be reduced.

According to an embodiment, the microstructure formed on the electrode may include an embossed structure of an embossed shape having a three-dimensional structure of a cylindrical shape or a cylindrical shape or a three-dimensional shape, or an intaglio structure of an intaglio shape.

In one embodiment, the microstructure having a sucker shape mimics an adhesion system of mollusks such as octopus, for example, a sucker shape, and the sucker shape may be nano-sized or micro-sized, and the diameter of the microstructure It may be 1 μm to 100 μm, and the height (or depth) of the microstructure may be 1 μm to 100 μm, and its aspect ratio may be 2/3 to 3.

In one embodiment, the base surface of the sucker includes a hill-shaped embossed portion, and the height of the hill-shaped embossed portion may be smaller than the depth of the sucker chamber.

In one embodiment, the shape of the hill-shaped embossed portion may be greater than the circumference of the upper and lower circumference of the middle portion of the body.

In one embodiment, the size of the circumference of the hill-shaped embossed portion is smaller than the circumference of the sucker chamber, and is attached to the surface to be adhered to the hill-shaped embossed state without pressing the rear surface of the electrode for adsorption to the sucker chamber. The longest circumferential surface of the portion does not contact the circumference of the sucker chamber, and may be configured such that the longest circumferential surface adheres to the inner surface of the sucker chamber when the rear surface of the electrode is pressed.

In one embodiment, the intaglio structure is a cylindrical shape, and the hill-shaped embossed portion may be a spherical or hemispherical shape protruding from the base surface of the intaglio structure.

In one embodiment, the spacing between the plurality of microstructures may be 1:1 to 1:3 with respect to the diameter of the sucker shape.

In one embodiment, the size of the circumference of the hill-shaped embossed portion is smaller than the circumference of the sucker chamber, and is attached to the surface to be adhered to the hill-shaped embossed state without pressing the rear surface of the electrode for adsorption to the sucker chamber. The longest circumferential surface of the portion does not contact the circumference of the sucker chamber, and may be configured such that the longest circumferential surface adheres to the inner surface of the sucker chamber when the rear surface of the electrode is pressed. For example, the bio-adhesive electrode may be to adhere the adhesive surface to the skin adhesion surface and pressurize it.

In one embodiment, the bio-adhesive electrode may be adhered even in a humid environment. In other words, the bio-adhesive electrode may be attached to a skin adhesion surface having a humid environment.

In one embodiment, the humid environment may be an environment in which water is present on the surface to be adhered. For example, it may be an environment in which water or liquid is present.

Although not limited thereto, for example, it may be an environment in which at least a portion of water is present, based on an area of 1 X 1 cm of the surface to be adhered. Alternatively, the humid environment may be an environment in which water is applied to 100 ul or more based on an area of 3X3 cm. For example, the humid environment may be an environment in which 200ul of water is applied based on an area of 3X3cm to be adhered.

Conventional adhesive sensors have difficulty in using the sensor in a wet environment because it is difficult to adhere in a humid environment, but the Saint-Adhesive electrode of the present invention is characterized by being well adhered and sensed even in a humid environment. In addition, the bio-adhesive electrode of the present invention is a sensor and has a structure capable of adhesion at the same time, and is easy to detach and attach. It is less irritating or contaminating, and can be well attached to wet environments, especially living surfaces, and human skin, and can be easily and safely applied.

In one embodiment, the bio-adhesive electrode can be easily adhered to and easily separated from the skin adhesion surface having a dry environment, and at the same time, can be easily adhered to and easily separated from the skin adhesion surface having a wet environment unlike the conventional one. .

In one embodiment, the adhesive force of the bio-adhesive electrode is due to the van der Waals force between the electrode and the surface to be adhered, capillary force according to moisture that may be present on the surface to be adhered, and suction force due to pressure difference inside and outside the sucker. May be In the case of the conventional dry bonding, only the van der Waals force is used, but in the case of the present invention, an additional other force is added in addition to the van der Waals force, so that the adhesive strength is excellent regardless of the humidity of the surface to be adhered.

In one embodiment, the bio-adhesive electrode may have a better sensing effect than a conventional sensor. In particular, it is well attached to a humid environment, a wet skin surface or a wet surface, for example, a living body surface and a human skin, to sense an electrical signal.

In one embodiment, the bio-adhesive electrode may be used for a drug delivery patch, for example, a drug may be carried in the sucker of the electrode.

In one embodiment, the bioadhesive electrode may be applied to a sensor that measures bioelectrical signals. In one embodiment, the bio-adhesive electrode may be used as various bio-sensors. Although not limited thereto, for example, the bio-adhesive electrode may be used as a pressure sensor on the skin, a motion sensor of the body, and an electrocardiogram sensor.

1 is a schematic diagram showing a bio-adhesive electrode according to an embodiment of the present invention. 1, the stretchable dry adhesive electrode of the present invention is stretchable and conductive, including a plurality of microstructures (engraved structures, engraved suckers), for example, a conductive material including an octopus imitation pattern (sucker chamber pattern). It may be a patch made of a polymer having a. Referring to FIG. 1, an intaglio structure pattern is constantly formed on an adhesive surface of the electrode, and an embossed portion such as a hemispherical shape is formed in the cavity of the intaglio structure.

The wearable device of the present invention includes the bioadhesive electrode of the present invention.

The bio-adhesive electrode manufacturing method of the present invention includes a first step of pouring a composite solution in which an organic solvent, a conductive material, an elastic polymer and a dispersant are mixed into a pattern mold; And a second step of curing the composite solution to prepare an electrode including a composite having a pattern.

In one embodiment, the organic solvent includes at least one of chloroform, n-hexane (Hexane), DMF (Dimethylformamide), toluene, NMP (N-Methylpyrrolidone), acetone and mixtures thereof. It can be done.

In one embodiment, in the first step, the composite solution is prepared by mixing a first mixed solution comprising a first organic solvent, a conductive material and a dispersant, and a second mixed solution containing a second organic solvent and an elastic polymer. May be

In one embodiment, the pattern mold may be manufactured using a partial filling technique.

Example: pattern mold production

2 is a view showing a pattern mold manufacturing method of the present invention according to an embodiment. As shown in FIG. 2, a pattern mold of the present invention was prepared according to one embodiment.

First, through a partial filling technique, which is a technique of forming a pattern in a state in which air bubbles are trapped in a hole pattern, a first mold having a shape in which a cylindrical upper portion is dug in a hemispherical shape is formed on a silicon surface. Did. Then, a polyurethane precursor (PUA precursor), which is a polymer precursor, was poured into the first mold, and then the PET film was uniformly covered by pushing the PET film from one end with a roller. At this time, air bubbles are trapped inside the hole pattern. Then, the polymer precursor was cured by performing a UV curing process (UV exposure), and the cured polymer was separated from the first mold to prepare an octopus-mimicking polymer pattern mold (Polymeric mater).

Example: Preparation of a bio-adhesive sensor

3 is a view showing a method of manufacturing a bio-adhesive sensor of the present invention according to an embodiment. As shown in Figure 3, according to one embodiment, the bio-adhesive sensor of the present invention was prepared.

First, carbon black as a conductive material particle in chloroform or n-hexane, and P3HT as a dispersant were dispersed in a vortex mixer for 10 minutes. Then, it was dispersed evenly by sonication for 30 minutes. Then, the elastic polymer was also diluted in chloroform or n-hexane and dispersed with a vortex mixer for 10 minutes.

Next, each of the two solutions was mixed and sonicated again for 30 minutes to prepare a precursor solution (composite solution) of the elastic polymer composite electrode containing the conductive material. The complex solution was poured into the pattern mold as shown in FIG. 3. Thereafter, the organic solvent was evaporated using a vacuum pump for 30 minutes to remove air bubbles.

Then, it was cured in an oven at 85° C. for 2 hours, and the pattern mold was separated to prepare an elastic polymer composite electrode (bio-adhesion sensor) comprising a conductive material having an octopus-like pattern.

4 is a view showing the results of the adhesion test of the bio-adhesive electrode according to an embodiment of the present invention. Referring to Figure 4, the case where the pattern is formed, as in the present invention, showed excellent adhesion compared to the case where there is no pattern. In addition, when the adhesion test was performed on the silicon wafer, the adhesion was significantly better in a dry environment than in a humid environment (a and b). In the case of the adhesion test to the biological skin, the adhesion was best in a dry environment, but the adhesion was more excellent in the case of the bio-adhesive electrode having the pattern of the present invention even in a humid environment (c). At this time, the dry environment is adhered by the van der Waals force and the suction effect, and the wet environment can be adhered by the capillary force and the suction effect. After all, if there is a pattern, the suction effect is additionally generated, and thus a higher adhesive strength can be exhibited. As a result of repeatedly desorption of the electrode of the present invention on the skin of the body (d), it can be seen that it shows excellent adhesive strength even after repeated desorption. As a result, it can be seen through FIG. 4 that the adhesion is improved through the structure.

5 is a view showing the electrical property test results of the bio-adhesive electrode according to an embodiment of the present invention. Referring to FIG. 5, electrical signal changes (resistance changes) according to tensile strain and carbon black concentration are shown (a). Through these results, it can be seen that the smaller the concentration of carbon black, the more sensitive it can be to small tensile strain. And, when the concentration of carbon black is 1.0 vol%, the resistance change with pressure is shown (b). 5, it is possible to confirm the concentration of the conductive material capable of sensing the tensile strain or pressure more sensitively. Referring to a of FIG. 5, in the case of 7.0 vol%, it can be confirmed that the resistance hardly changes until the strain is 60%. Through these features, the bio-adhesive electrode of the present invention having a carbon black concentration of 7.0 vol% seems to be useful as a flexible electrode. In addition, when looking at b of FIG. 5, it can be seen that the sensitivity is highest when the concentration of carbon black is 1.0 vol%.

6 is a view showing the results of a biosensing experiment of a bioadhesive electrode according to an embodiment of the present invention. Specifically, FIG. 6 shows an actual attachment state (a), an electrocardiogram measurement result (b), and an elasticity measurement result (c) of the bioadhesive electrode of the present invention manufactured according to an embodiment. Looking at the actual attached state, it can be seen that the electrode of the present invention was well adhered to the skin even in a dry environment, and well attached in a humid environment. At this time, the humid environment is a condition in which 200ul of water is applied based on an area of 3X3cm. As a result of the experiment, although the electrical signal change is relatively low in a wet state than in a dry environment, it can be seen that electrocardiogram and motion measurement using the bioadhesive electrode of the present invention is sensed regardless of humidity.

Although described above with reference to the preferred embodiments of the present invention, those skilled in the art may variously modify and change 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.

Claims (16)

It consists of an elastic polymer containing a conductive material,
A part of the surface contains a plurality of microstructures,
The microstructure is characterized in that the sucker chamber of the intaglio shape dug from the surface, for measuring or sensing a bio-signal,
Dry adhesive skin patch. According to claim 1,
The conductive material comprises at least one of carbon black, carbon nano tube (CNT), graphene flake graphite, and graphene. ,
Dry adhesive skin patch. According to claim 1,
The elastic polymers include natural rubber, nitrile rubber, acrylonitrile-butadiene rubber, styrenebutadienerubber, chloroprene rubber, and butyl rubber , Isoprene isobutylene rubber, ethylene propylene rubber, chlorosulphonated polyethylene rubber, acrylic rubber, fluoro rubber, polysulfide Polysulfide rubber, silicone rubber, butadiene rubber, isoprene rubber, urethane rubber, polyurethane, polydimethylsiloxane (PDMS), polyolefin thermoplastic elastomer ( polyolefin thermoplastic elastomer, TPE, polystyrene TPE, polyvinyl chloride TPE, polyester TPE, polyurethane TPE, polyamide TPE, and the like. Characterized in that it comprises at least one of the mixture of,
Dry adhesive skin patch. According to claim 1,
Includes a hill-shaped embossed portion on the base surface of the sucker,
The height of the hill-shaped embossed portion, characterized in that less than the depth of the sucker chamber,
Dry adhesive skin patch. The method of claim 4,
The shape of the hill-shaped embossed portion is characterized in that the circumference of the middle portion of the trunk is larger than the circumference of the top and bottom,
Dry adhesive skin patch. The method of claim 4,
The microstructure is a cylindrical shape,
The hill-shaped embossed portion is characterized in that the spherical or hemispherical shape protruding from the base surface,
Dry adhesive skin patch. The method of claim 5,
The diameter of the cylinder is 1㎛ to 100㎛,
The height of the cylinder is characterized in that 1㎛ to 100㎛,
Characterized in that the aspect ratio is 2/3 to 3,
Dry adhesive skin patch. The method of claim 4,
Arrangement interval of the plurality of microstructures, characterized in that 1:1 to 1:3 with respect to the diameter of the sucker,
Dry adhesive skin patch. The method of claim 4,
The size of the circumference of the hill-shaped embossed portion is smaller than the circumference of the sucker chamber,
The longest circumferential surface of the hill-shaped embossed portion does not contact the circumference of the sucker chamber when it is attached to the surface to be adhered and the back surface of the electrode is not pressed for adsorption to the sucker chamber.
When the rear surface of the electrode is pressed, the longest circumferential surface is configured to adhere to the inner surface of the sucker chamber,
Dry adhesive skin patch. According to claim 1,
The electrode has a carbon black concentration of 4.0 vol% or more,
The biosignal is an electrical signal generated from the living body,
The skin patch is for measuring electrical signals from a living body,
Dry adhesive skin patch. The method of claim 10,
The dry adhesive skin patch is maintained on the skin in a humid environment, the adhesion is maintained, the electrical signal measurement rate is not reduced,
Dry adhesive skin patch. According to claim 1,
The electrode has a carbon black concentration of 4.0 vol% or less,
The biological signal is a physical signal generated from a living body,
The skin patch is a physical signal from the living body to sense the change in the resistance value,
Dry adhesive skin patch. The method of claim 12,
The dry adhesive skin patch maintains adhesion in skin having a humid environment, and provides an amplified sensing rate than in the case where the microstructure is not present.
Dry adhesive skin patch. An electrode for health monitoring including the black adhesive skin patch of any one of claims 1 to 10. Electrode for ECG (electrocardiogram) comprising the black adhesive skin patch of any one of claims 1 to 10. A pulse or heart rate measuring sensor comprising the black adhesive skin patch of any one of claims 1 to 10.

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