KR102176764B1 - Adhesive transparent electrode and method for manufacturing thereof - Google Patents

Abstract

The present invention relates to an adhesive transparent electrode and a method of manufacturing the same, wherein the adhesive transparent electrode according to an embodiment of the present invention includes a substrate, and an adhesive polydimethylsiloxane (PDMS) embedded with a silver (Ag) nanowire network deposited on the substrate. A matrix, wherein the tacky polydimethylsiloxane matrix includes polydimethylsiloxane including a polydimethylsiloxane basd and a polydimethylsiloxane curing agent and a nonionic surfactant.

Description

Adhesive transparent electrode and its manufacturing method {ADHESIVE TRANSPARENT ELECTRODE AND METHOD FOR MANUFACTURING THEREOF}

The present invention relates to an adhesive transparent electrode and a method of manufacturing the same, and more particularly, a silver nanowire network is embedded in an adhesive polydimethylsiloxane (PDMS) matrix containing a nonionic surfactant to improve compliance and adhesiveness, and It relates to a method of manufacturing the same.

Recently, due to the development of the Internet of Things (IoT) and interest in well-being, interest and research on wearable electronic devices are increasing.

In particular, in the case of a biosensor that is attached to the body to detect movement of the body or detects a biological signal, it is very important to develop a sticky electrode material because it must be well attached to the body. In addition, in the case of a biosensor using an electric signal, a process of forming an electrode on a substrate is required. If such additional processes are reduced, the cost of the process can be greatly reduced.

On the other hand, techniques for controlling physical properties of polydimethylsiloxane to have adhesiveness and high ductility by mixing an additive with polydimethylsiloxane have been reported. The most reported method is the use of a silicone-based additive similar to polydimethylsiloxane. However, when a silicone-based additive is used, an excessive amount of additive is required, and the viscosity of the solution increases due to the additive, causing difficulties during the solution process.

In addition, recently, studies on controlling physical properties of polydimethylsiloxane to have adhesiveness and high ductility by using ethoxylated polyethyleneimine (PEIE), which is an amine-based polymer, have been reported. However, in the case of using ethoxylated polyethyleneamine, residues remain on the surface during separation after adhesion, and there is a problem in that light transmittance decreases due to internal moisture because hygroscopicity is very high.

In addition, all of the above-mentioned methods of changing the physical properties of polydimethylsiloxane are studies that only change the physical properties of the polydimethylsiloxane material.To form an electrode for manufacturing an electronic device, all electrodes are formed through an additional coating or deposition process. You have to go through a separate process.

Therefore, even with a small amount of additives, the physical properties of polydimethylsiloxane can be easily controlled, the difference in transmittance is not large compared to the existing polydimethylsiloxane, and the viscosity of the liquid before curing is not high, so it is necessary to develop a new technology that facilitates the process.

Embodiments of the present invention are intended to provide an adhesive transparent electrode capable of easily controlling the physical properties of polydimethylsiloxane with only a very small amount of nonionic surfactant by using a nonionic surfactant, and a method of manufacturing the same.

Embodiments of the present invention are to provide an adhesive transparent electrode and a method for manufacturing the same, which can be attached to the skin without an additional adhesive due to the high adhesiveness of the transparent electrode according to the embodiment of the present invention, and that can maintain the adhesiveness even after several times of detachment and detachment.

The embodiments of the present invention provide an adhesive transparent electrode capable of manufacturing a transparent electrode at the same time as the curing of polydimethylsiloxane, unlike the conventional method of forming an electrode on a cured polymer substrate through other coating treatments, and a method for manufacturing the same. I want to.

Embodiments of the present invention are intended to provide an adhesive transparent electrode capable of maintaining electrical conductivity even at a high strain due to the electrical characteristics of a silver nanowire network, and a method of manufacturing the same.

An adhesive transparent electrode according to an embodiment of the present invention includes a substrate and an adhesive polydimethylsiloxane matrix in which a silver (Ag) nanowire network deposited on the substrate is embedded, and the adhesive polydimethylsiloxane matrix is a polydimethylsiloxane matrix ( base) and polydimethylsiloxane and nonionic surfactants including a polydimethylsiloxane curing agent.

The adhesive transparent electrode according to an embodiment of the present invention is a crosslinking reaction of the polydimethylsiloxane due to the interaction of the platinum (Pt) catalyst present in the polydimethylsiloxane curing agent and the polar functional group present in the nonionic surfactant. ) Is hindered, and mechanical properties of the adhesive polydimethylsiloxane matrix may be improved.

The tacky transparent electrode according to an embodiment of the present invention has the silver nanowire network in the tacky polydimethylsiloxane matrix due to the interaction between the polar functional group present in the nonionic surfactant and the polar functional group present in the silver nanowire network. Can be embedded.

In the adhesive transparent electrode according to an embodiment of the present invention, the nonionic surfactant may be 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol.

The adhesive transparent electrode according to an exemplary embodiment of the present invention may have a weight ratio of 10:1:0.01 to 10:1:0.08 in the polydimethylsiloxane base, the polydimethylsiloxane curing agent, and the nonionic surfactant.

The method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention comprises the steps of forming a silver nanowire network on a substrate, a polydimethylsiloxane motif, a polydimethylsiloxane curing agent, and a nonionic interface on the substrate on which the silver nanowire network is formed. Coating a dispersion containing an activator, and thermosetting the dispersion coated on the substrate on which the silver nanowire network is formed, thereby forming an adhesive polydimethylsiloxane matrix in which the silver nanowire network is embedded.

The method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention may further include separating the adhesive polydimethylsiloxane matrix in which the silver nanowire network is embedded from the substrate.

In the method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention, the forming of a nanowire network on the substrate comprises: coating a silver nanowire solution on the substrate; And annealing the substrate coated with the silver nanowire solution.

In the method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention, the substrate coated with the silver nanowire solution may be annealed at 100° C. to 180° C. for 5 minutes to 20 minutes.

In the method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention, the dispersion coated on the substrate on which the silver nanowire network is formed may be heat cured at 40°C to 80°C.

According to an embodiment of the present invention, by using a nonionic surfactant, the physical properties of polydimethylsiloxane can be easily controlled with only a very small amount of nonionic surfactant.

In addition, according to the exemplary embodiment of the present invention, the transparent electrode according to the exemplary embodiment of the present invention has high adhesiveness, so that it can be attached to the skin without an additional adhesive, and the adhesiveness can be maintained even after several times of detachment.

In addition, according to an embodiment of the present invention, unlike a conventional method of forming an electrode on a cured polymer substrate through other coating treatments, etc., a transparent electrode can be manufactured simultaneously with thermal curing of polydimethylsiloxane.

In addition, according to an embodiment of the present invention, due to the electrical characteristics of the silver nanowire network, it is possible to maintain electrical conductivity even at a high strain.

1 is a view showing a method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention.
2A to 2E show images of the tacky polydimethylsiloxane matrix according to the content of Triton x-100 in the tacky polydimethylsiloxane matrix according to an embodiment of the present invention, and FIG. 2F is a triton x- in the tacky polydimethylsiloxane matrix. It is a graph showing the light transmittance according to the 100 content.
3A is a graph showing a stress-strain curve of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, and FIG. 3B is a graph showing a uniaxial stretching test of a4-PDMS_40. It shows a picture.
4 is a graph showing the viscoelasticities of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention.
Figure 5a is a graph showing the adhesion (adhesion force) measured by the peel test (peel test) of the adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, Figures 5b to 5h are adhesion measured by the peel test Is a graph showing, and FIG. 5i shows an image of an adhesive polydimethylsiloxane matrix supporting various weights.
6A and 6B are graphs showing a swelling ratio of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, and FIGS. 6C and 6D are graphs showing a gel fraction.
7A and 7B are graphs showing cell viability for measuring the biocompatibility of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention and an optical microscope image of fibroblasts, and FIG. 7C is an absorbance of fibroblasts. It is a graph showing.
8 is a graph showing the light transmittance of an adhesive transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention.
9A is a graph showing the results of performing an elasticity test to evaluate the elasticity of an adhesive transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention, and FIGS. 9B to 9E are It shows a field emission-scanning electron microscope (FE-SEM, Field Emission-Scanning Electron Microscopy) image before and after stretching.
FIG. 10A is a photograph illustrating a case of attaching a deformation sensor to a wrist to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIG. 10B is A picture of a case where a deformation sensor to which a polydimethylsiloxane matrix-based adhesive transparent electrode (PDMS_40NW) is applied is attached to a wrist according to an embodiment of the present invention. Figure 10c is a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires and a transparent electrode (PDMS_40NW) based on a polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention. It is a graph showing the relative resistance change of the applied strain sensor.
11A to 11C are an adhesive polydimethylsiloxane matrix-based transparent electrode (a4-PDMS_40NW) embedded with silver nanowires and a polydimethylsiloxane matrix-based adhesive transparent electrode embedded with silver nanowires according to an embodiment of the present invention ( PDMS_40NW) is a photograph of an ECG sensor applied to each arm attached to each arm, and FIG. 11D is a graph showing skin impedance measured using the ECG sensor.
12A is a view showing the electrode position of an ECG sensor to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIGS. 12B to 12E are ECG sensors It is a graph showing the ECG signal measured by.
13A to 13D show electrode positions of an ECG sensor to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIGS. 13B to 13D Is a graph showing the ECG signal measured by the ECG sensor.

Hereinafter, embodiments of the present invention will be described in detail with reference to the accompanying drawings and contents described in the accompanying drawings, but the present invention is not limited or limited by the embodiments.

The terms used in this specification are for describing exemplary embodiments, and are not intended to limit the present invention.

The terms "comprises," "have," or "have" as used herein are intended to designate the presence of features, numbers, steps, actions, components, parts, or combinations thereof described in the specification, It is to be understood that the possibility of the presence or addition of one or more other features or numbers, steps, actions, elements, parts, or combinations thereof is not preliminarily excluded.

In addition, as used herein, "an embodiment", "example", "side", "example", and the like are described as having any aspect or design that is better or advantageous than other aspects or designs. It does not have to be interpreted.

In addition, the term "or" used herein refers to an inclusive OR "inclusive or" rather than an exclusive OR "exclusive or". That is, unless stated otherwise or unless clear from context, the expression “x uses a or b” means any one of natural inclusive permutations.

In addition, the singular expression ("a" or "an") used in the present specification should be generally interpreted as meaning "one or more" unless otherwise stated or unless it is clear from the context that it relates to the singular form. do.

In addition, in the present specification, when a portion such as a film, layer, region, component, etc. is said to be “on” or “on” another portion, not only the case directly above the other portion, but also another film, layer, region in the middle thereof This includes cases where components, etc. are interposed.

In addition, in this specification, terms such as "first" or "second" may be used to describe various elements, but the elements should not be limited by the terms. The terms are only for the purpose of distinguishing one component from other components, for example, without departing from the scope of rights according to the concept of the present invention, the first component may be referred to as the second component, Similarly, the second component may also be referred to as a first component.

Unless otherwise defined, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which the present invention belongs. Terms as defined in a commonly used dictionary should be interpreted as having a meaning consistent with the meaning of the related technology, and should not be interpreted as an ideal or excessively formal meaning unless explicitly defined in this specification. Does not.

Hereinafter, specific embodiments of the present invention will be described in detail with reference to the drawings. However, the spirit of the present invention is not limited to such an embodiment, and the spirit of the present invention may be proposed differently by addition, change and deletion of components constituting the embodiment, but this is also included in the spirit of the invention. It becomes.

The present invention relates to an adhesive transparent electrode and a method for manufacturing the same, and to a transparent electrode having excellent ductility and adhesiveness by adding an additive (nonionic surfactant) to polydimethylsiloxane, and a method of manufacturing the same.

1 is a view showing a method of manufacturing an adhesive transparent electrode according to an embodiment of the present invention.

Referring to FIG. 1, an adhesive transparent electrode according to an embodiment of the present invention may be manufactured using a substrate, polydimethylsiloxane, a nonionic surfactant, and a silver nanowire network.

After coating 130a of the silver nanowire solution 120 on the substrate 110, the silver nanowire network 150 may be formed on the substrate 110 through annealing 140a.

The substrate 110 may include a transparent material capable of transmitting light, and may include, for example, a silicon substrate, a glass substrate, or a polymer substrate, but is not limited thereto.

The silicon substrate may include a single silicon substrate or a p-Si substrate, and the glass substrate may be formed of any one or a combination of alkali silicate-based glass, alkali-free glass, or quartz glass, but is limited thereto. Not, and can be made of various materials.

The polymer substrate may be made of any one of polyethylene terephthalate (PET), polyethylene naphtalate (PEN), polyimide (PI), and polyurethane, or a combination thereof, It is not limited thereto, and may be made of various materials. However, the polymer substrate is not limited thereto as long as it has transparency and flexibility enough to be used for a transparent flexible display.

The silver nanowire solution 120 may be coated on the substrate by a spin-coating method, but is not limited thereto, and the rotation speed and time may be different, and other known coating methods may be used. have.

Specifically, methods such as spin coating, spray coating, inkjet coating, slit coating, or deep coating can be used, but the method is special. It is not limiting.

After coating the silver nanowire solution 120 on the substrate 110 by spin coating at 400 rpm to 1000 rpm for 30 to 60 seconds (130a), an annealing 140a is performed to evaporate and dry the solvent.

Specifically, the silver nanowire network 150 may be formed by annealing at 100° C. to 180° C. for 5 minutes to 20 minutes.

Thereafter, a dispersion 160 including a polydimethylsiloxane base, a polydimethylsiloxane cross-linker, and a nonionic surfactant is coated on the substrate 110 coated with the silver nanowire network 150. .

The dispersion 160 may be prepared by mixing a polydimethylsiloxane base, a polydimethylsiloxane curing agent, and a nonionic surfactant in a weight ratio of 10:1:0.01 to 10:1:0.08, and preferably 10:1:0.03 to 10 It can be prepared by mixing in a weight ratio of :1:0.05.

The polydimethylsiloxane motif may be a commercially available product, and may be represented by the following formula (1).

[Formula 1]

The polydimethylsiloxane curing agent may be a material represented by Formula 2 below.

[Formula 2]

Nonionic surfactants are 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol (4-(1,1,3,3-Tetramethylbutyl)phenyl-polyethylene glycol), fatty alcohol-polyoxyethylene Ether (fatty alcohol-polyoxyethylene ether), polyoxyethylene sorbitan fatty acid esters, polyoxyethylene faty acid ester, polyoxyethylene alkylether, sorbitan ester ( sorbitan esters), glyceryl esters, glyceryl monostearate, polyethylene glycol, polypropylene glycol, polypropylene glycol esters, cetyl alcohol alcohol), cetostearyl alcohol, stearyl alcohol, or a combination thereof, but is not limited thereto, and may be made of various materials.

Preferably, the nonionic surfactant is 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol [4-(1,1,3,3-Tetramethylbutyl)phenyl- represented by the following formula (3). polyethylene glycol].

[Formula 3]

The dispersion liquid 160 may remove air bubbles in the composition through degassing, and the physical properties of the dispersion 160 may be controlled through a nonionic surfactant included in the dispersion 160.

The dispersion 160 may be coated on the substrate 110 coated with the silver nanowire network 150 by a spin-coating method, but is not necessarily limited thereto, and the rotation speed and time may be different. , Other known coating methods may be used.

Specifically, methods such as spin coating, spray coating, inkjet coating, slit coating, or deep coating can be used, but the method is special. It is not limiting.

After coating the dispersion 160 on the substrate 110 coated with the silver nanowire network 150 at 3 rpm to 400 rpm for 15 seconds to 30 seconds through spin coating (130b), thermal curing (140b) is performed. do.

Specifically, the adhesive polydimethylsiloxane matrix 170 in which the silver nanowire network 150 is embedded may be formed by heat curing at 40° C. to 80° C. for 9 to 11 hours.

Thereafter, when the thermosetting adhesive polydimethylsiloxane matrix 170 is removed from the substrate 110, the adhesive transparent electrode 100 in which the silver nanowire network is embedded is formed.

The adhesive transparent electrode based on the adhesive polydimethylsiloxane matrix according to the embodiment of the present invention is obtained by thermally curing polydimethylsiloxane, unlike the conventional method of forming an electrode through other coating treatment on a thermosetting polymer substrate. After separation from the substrate, since the silver nanowire network exists on the surface of the polydimethylsiloxane matrix, it can be simply formed without an additional process of forming an electrically conductive material.

Hereinafter, characteristics of an adhesive polydimethylsiloxane matrix and an adhesive transparent electrode based on the adhesive polydimethylsiloxane matrix according to an embodiment of the present invention will be described.

(Example)

(Preparation of dispersion)

The dispersion is a polydimethylsiloxane base, a polydimethylsiloxane curing agent, and 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol (hereinafter referred to as Triton x-100). It was prepared by mixing in various weight ratios of: 1: 0 to 10: 1: 0.08.

The weight ratio of the polydimethylsiloxane main agent and the polydimethylsiloxane curing agent was fixed at 10:1.

(Manufacture of adhesive transparent electrode)

A slide glass (Paul Marienfeld GmbH & Co. KG, Germany) to be used as a substrate was sequentially washed in a sonication bath for 10 minutes each using acetone, 2-propanol, and deionized water, and then dried using an air gun.

A 0.65 wt% silver nanowire solution (Novarials) having an average length of 30 nm and a diameter of 30 nm was spin-coated on the substrate at 500 rpm for 60 seconds, and then annealed at 100° C. for 5 minutes to evaporate the solvent. .

The dispersion was spin-coated on the substrate coated with the silver nanowire solution at 300 rpm for 15 seconds, and then thermally cured at a temperature of 40° C. to 80° C. for 11 hours.

Thereafter, the cured adhesive polydimethylsiloxane matrix was immersed in a deionized water bath for 5 minutes at room temperature, and then the adhesive transparent electrode embedded with the silver nanowire network was removed from the substrate while immersed in deionized water.

(Comparative example)

(Preparation of dispersion)

The dispersion was prepared by mixing a polydimethylsiloxane base material and a polydimethylsiloxane curing agent in a weight ratio of 10:1.

(Manufacture of transparent electrode)

A slide glass (Paul Marienfeld GmbH & Co. KG, Germany) to be used as a substrate was sequentially washed in a sonication bath for 10 minutes each using acetone, 2-propanol, and deionized water, and then dried using an air gun.

A 0.65 wt% silver nanowire solution (Novarials) having an average length of 30 nm and a diameter of 30 nm was spin-coated on the substrate at 500 rpm for 60 seconds, and then annealed at 100° C. for 5 minutes to evaporate the solvent. .

The dispersion was spin-coated on the substrate coated with the silver nanowire solution at 300 rpm for 15 seconds, and then thermally cured at a temperature of 40° C. to 80° C. for 11 hours.

After that, the heat-cured polydimethylsiloxane matrix was immersed in a deionized water bath for 5 minutes at room temperature, and then the polydimethylsiloxane matrix embedded with the silver nanowire network was removed from the substrate while immersed in deionized water.

In order to examine the characteristics of the adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, the weight% and curing temperature (T _c ) of Triton x-100 in the adhesive polydimethylsiloxane matrix were changed, and the samples used were shown in the following [Table] Same as 1].

Sample name % By weight of Triton x-100 in the tacky polydimethylsiloxane matrix Heat curing temperature (T _c ) ( ^o C) PDMS_40
0 40 PDMS_70 70 a3-PDMS_40
0.3 40 a3-PDMS_50 50 a3-PDMS_70 70 a4-PDMS_40
0.4 40 a4-PDMS_50 50 a4-PDMS_70 70 a5-PDMS_40 0.5 40 a8-PDMS_40 0.8 40

2A to 2E show images of the tacky polydimethylsiloxane matrix according to the content of Triton x-100 in the tacky polydimethylsiloxane matrix according to an embodiment of the present invention, and FIG. 2F is a triton x- in the tacky polydimethylsiloxane matrix. It is a graph showing the light transmittance according to the content of 100. Referring to Figs. 2A to 2E, the contents of Triton x-100 in the adhesive polydimethylsiloxane matrix are 0%, 0.3%, and 0.4%, respectively, when the thermal curing temperature is 40°C. , 0.5%, and 0.8%, and it can be seen that light scattering of the sticky polydimethylsiloxane matrix increases as the content of Triton x-100 increases.

Referring to Figure 2f, it can be seen that the light transmittance (T) of the adhesive polydimethylsiloxane matrix decreases as the content of Triton x-100 increases, and the thermal curing temperature (T) for the light transmittance of the adhesive polydimethylsiloxane matrix It can be seen that the effect of _c ) is almost negligible.

The polydimethylsiloxane matrix (PDMS_40) not mixed with Triton x-100 has the highest light transmittance value of 94.3% at a wavelength of 550 nm. The light transmittance of the tacky polydimethylsiloxane matrix obtained by mixing 0.3% by weight of Triton x-100 (hereinafter referred to as a3-PDMS_40) and 0.4% by weight of Triton x-100 (hereinafter referred to as a4-PDMS_40) was respectively obtained. It can be seen that the light transmittance is reduced to 91.4% and 84.7% compared to PDMS_40.

In order to manufacture a transparent electrode based on an adhesive polydimethylsiloxane matrix, the light transmittance of the adhesive polydimethylsiloxane matrix should be 80% or more. Therefore, a3-PDMS_40 and a4-PDMS_40 were selected for later analysis.

The reason why the light transmittance decreases as the content of Triton x-100 increases is due to scattering of light due to the micelle structure formed in the polydimethylsiloxane matrix mixed with Triton x-100. Since the polydimethylsiloxane matrix is very hydrophobic, the triton x-100 chain alkyl forms a shell, whereas the corresponding polyethylene glycol (PEG) moiety forms a micelle structure core. do.

In addition, it is known that the light scattering intensity increases as the size of the micelle increases as the concentration of the surfactant increases.

3A is a graph showing a stress-strain curve of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, and FIG. 3B is a graph showing a uniaxial stretching test of a4-PDMS_40. It shows a picture.

The Young's modulus and failure strain of the polydimethylsiloxane matrix and the sticky polydimethylsiloxane matrix were 0.3% by weight of Triton x prepared by changing the thermal curing temperature to 40°C, 50°C and 70°C, respectively. Only samples containing -100 and 0.4% by weight of Triton x-100 were measured.

In addition, the tensile speed was fixed at 1 mm·sec ^-1 , the temperature was maintained at 20°C, and the Young's modulus was calculated as a strain from 0% to 100%.

Samples for measuring Young's modulus and breaking strain of the polydimethylsiloxane matrix and the adhesive polydimethylsiloxane matrix, and the measurement results are shown in Table 2 below.

Sample Young's modulus (kPa) Breaking strain (%) PDMS_40 480 ± 30 230 a3-PDMS_40 38 ± 6.3 > 400 a4-PDMS_40 40 ± 5 > 400 a3-PDMS_50 194 ± 7.2 > 300 a4-PDMS_50 162 ± 20 > 300 a3-PDMS_70 1000 ± 50 220 a4-PDMS_70 810 ± 20 210

3A and [Table 2], it can be seen that a3-PDMS_40 and a4-PDMS_40 represent the lowest Young's modulus and the largest fracture strain among all samples. The Young's modulus and fracture strain of PDMS_40 are 500, respectively. kPa and 230%, in contrast, the Young's modulus of a3-PDMS_40 and a4-PDMS_40 were 38 kPa and 40 kPa, respectively, and both films showed a breaking strain of 400% or more.

The Young's modulus of a3-PDMS_40 and a4-PDMS_40 was much lower than that of 500 kPa to 1 MPa, which is the Young's modulus of human skin, from which it can be seen that a3-PDMS_40 and a4-PDMS_40 are suitable for epidermal electronics. .

As the Young's modulus of the polymer matrix decreases, the conformability of the electrode increases.When the adhesive polydimethylsiloxane matrix has a lower Young's modulus than the skin, the contact area between the electrode and the skin expands and the user feels uncomfortable. Can feel less.

In addition, referring to FIG. 3A, it can be seen that the Young's modulus increases as the thermal curing temperature of the adhesive polydimethylsiloxane matrix increases. Conventionally, the elastic modulus of the polydimethylsiloxane was lowered by reducing the amount of the polydimethylsiloxane curing agent, but there was a disadvantage in that the fracture deformation of the polydimethylsiloxane was also lowered.

In contrast, a3-PDMS_40 and a4-PDMS_40 show highly enhanced fracture strain, from which it can be seen that a3-PDMS_40 and a4-PDMS_40 are candidates suitable for application as transparent and stretchable polymer matrix of epidermal electrons. .

Referring to FIG. 3B, it can be seen that a4-PDMS_40 does not break even when deformation is greater than 400%.

4 is a graph showing the viscoelasticities of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention.

The viscoelasticity of the polydimethylsiloxane matrix and the tacky polydimethylsiloxane matrix was measured using a dynamic mechanical analyzer. In addition, the viscoelasticity of the polydimethylsiloxane matrix and the adhesive polydimethylsiloxane matrix is defined by the following formula (1).

tanδ is the loss tangent, E'represents the elasticity of the elastic body, and E" represents the viscoelasticity of the elastic body. Therefore, the higher the loss tangent (tanδ) of the elastic body, the more viscoelastic behavior is exhibited.

For reference, since a3-PDMS_40 and a4-PDMS_40 showed similar results in the uniaxial tensile test, only the viscoelasticity of the polydimethylsiloxane matrix and the tacky polydimethylsiloxane matrix containing 0.4% by weight of Triton x-100 was analyzed.

Referring to FIG. 4, it can be seen that the loss tangent decreases as the curing temperatures of PDMS_40, a4-PDMS_40, a4-PDMS_50, and a4-PDMS_70 decrease. Also, it can be seen that a4-PDMS_40 shows a high loss tangent value of about 0.5 even at a low frequency of 0.1 Hz.

In previous studies, the loss tangent value of the silicone rubber was found to be less than 0.4 or less than 0.1, and from this, it can be seen that a4-PDMS_40 exhibits very high viscoelasticity compared to other silicone-based elastomers.

Based on the above-described uniaxial tensile test and viscoelasticity measurement, the curing temperature is 40°C, and the tacky polydimethylsiloxane matrix to which 0.3% by weight of Triton x-100 or 0.4% by weight of Triton x-100 is added is triton x-100. It can be seen that it is more flexible and has higher viscoelasticity than the polydimethylsiloxane matrix without the addition.

Figure 5a is a graph showing the adhesion (adhesion force) measured by the peel test (peel test) of the adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, Figures 5b to 5h are adhesion measured by the peel test Is a graph showing, and FIG. 5i shows an image of an adhesive polydimethylsiloxane matrix supporting various weights.

The adhesion of the polydimethylsiloxane matrix and the tacky polydimethylsiloxane matrix was measured by a peel test according to the ASTM D3330 standard with a peel angle of 90°, and the test apparatus is shown in the inserted image of FIG. 5A.

The size of the sample for measuring the adhesion was 100 mm × 25 mm, the peel rate was fixed at 300 mm·min ^-1 , and the force of the load cell was 20 N. In addition, the test environment was maintained at 25±2° C. and 45±5% relative humidity.

5A, a3-PDMS_40 and a4-PDMS_40 exhibited the highest adhesion among all samples. It can be seen that the adhesion of a3-PDMS_40 is 35 Nm ^-1 , which is 7 times higher than that of the polydimethylsiloxane matrix.

5B to 5H, looking at the adhesion-distance of the sample measured by the peel test, it can be seen that the adhesion of a3-PDMS_40 and a4-PDMS_40 is the highest.

Referring to Figure 5i, using a4-PDMS_40, each 7.7g of coins, 30g of brass block, and 50g of brass block were attached to the finger. As a result, a4-PDMS_40 is a brass block having a weight of 50g. You can see that you can keep it.

From FIGS. 5A to 5I, it can be seen that the heat curing temperature affects the adhesion of the tacky polydimethylsiloxane matrix. The very low modulus and viscoelasticity of the tacky polydimethylsiloxane matrix heat-cured at 40°C improves the wetting and spreading of the polymer chain in the tacky polydimethylsiloxane matrix, thereby improving the surface contact, and the adhesion of the tacky polydimethylsiloxane matrix. It can be seen that this is improved.

6A and 6B are graphs showing a swelling ratio of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention, and FIGS. 6C and 6D are graphs showing a gel fraction.

The optical properties of the tacky polydimethylsiloxane matrix are greatly affected by the content of Triton x-100, and the mechanical properties such as Young's modulus, breaking strain, viscoelasticity and adhesion have a great influence on the thermosetting temperature of the tacky polydimethylsiloxane matrix. Receive.

As described above, in order to explain the effect of the content of Triton x-100 on Young's modulus, viscoelasticity and adhesion, the expansion ratio and gel fraction of the adhesive polydimethylsiloxane matrix and the polydimethylsiloxane matrix were measured, and chloroform and Toluene was used.

6A and 6B, it can be seen that the expansion ratio of a4-PDMS_40 is 2.5 times and 2 times higher in chloroform and toluene than that of PDMS_40, respectively.

In addition, referring to Figures 6c and 6d, it can be seen that the gel fraction of a4-PDMS_40 is 0.8 and 0.77 in chloroform and toluene, respectively, and PDMS_40 has values of 0.95 and 1.0 in chloroform and toluene, respectively.

Specifically, the swelling ratio in chloroform and toluene solvents represents the gel fractions of a4-PDMS and PDMS_40 as a function of curing temperature, and the swelling ratio and the gel fraction are defined by the following equations (2) and (3), respectively.

As shown in FIGS. 6A and 6B, the expansion ratio of a4-PDMS_40 is 2.5 times and 2 times higher than that of PDMS_40 when chloroform and toluene are used, respectively. Accordingly, the expansion ratio of the adhesive polydimethylsiloxane matrix decreases as the thermal curing temperature increases, and becomes similar to the expansion ratio of the adhesive polydimethylsiloxane matrix when the thermal curing temperature is 70°C or higher.

In addition, as shown in Figs. 6c and 6d, the gel fraction of a4-PDMS_40 is 0.8 and 0.77 in chloroform and toluene, respectively, and PDMS_40 has values of 0.95 and 1.0 in chloroform and toluene, respectively, and similar to the expansion ratio, adhesiveness The gel fraction of the polydimethylsiloxane matrix increases as the thermal curing temperature increases, and becomes similar to the polydimethylsiloxane matrix when the thermal curing temperature is 70°C or higher.

Crosslinking of polydimethylsiloxane occurs through hydrosilylation using a platinum (Pt) catalyst. The platinum catalyst diffuses through the polydimethylsiloxane matrix to complete the crosslinking reaction. Because the platinum catalyst is coordinarily unsaturated, it forms a complex with other polar functional groups, such as the PEG chain of Triton x-100.

In addition, Triton x-100 forms a core-shell structure inside the polydimethylsiloxane matrix. Therefore, when the non-polar functional group surrounds the platinum interacting polar group of the Triton x-100 core-shell structure inside the polydimethylsiloxane matrix, the amount of the active platinum catalyst present in the polydimethylsiloxane matrix is depleted.

Therefore, the crosslinking reaction is inhibited by adding a small amount of Triton x-100 to the polydimethylsiloxane mixture through deactivation of the platinum catalyst, which is the main mechanism for forming a heterogeneously crosslinked network in polydimethylsiloxane. By means of Triton x-100 molecules, a heterogeneously crosslinked network composed of crosslinked and non-crosslinked polydimethylsiloxanes is formed in the tacky polydimethylsiloxane matrix.

Such a composite structure forms a soft and tacky polydimethylsiloxane matrix by controlling mechanical properties such as Young's modulus, breaking strain, viscoelasticity and adhesion.

7A and 7B are graphs showing cell viability for measuring the biocompatibility of an adhesive polydimethylsiloxane matrix according to an embodiment of the present invention and an optical microscope image of fibroblasts, and FIG. 7C is an absorbance of fibroblasts. It is a graph showing.

Cell viability and proliferation for measuring the biocompatibility of the adhesive polydimethylsiloxane matrix (a4-PDMS_40 and a4-PDMS_70 in the sample used) and the polydimethylsiloxane matrix (PDMS_40 and PDMS_70 in the sample used) according to an embodiment of the present invention The speed was analyzed by an indirect method. Fibroblasts (L929) were grown in a 5% CO ₂ atmosphere incubator at 37°C. Samples were washed with ethanol and UV exposure. Then, the sample was placed in a 24-well plate, and 1 ml of a solution containing fibroblast cells was sprayed onto the sample.

The cell density of the solution was 105 cells·ml ^-1 , the cell viability was analyzed by the CCK-8 kit, and the absorbance was measured at 450 nm using a microplate reader (VersaMax, Molecular Devices LLC).

The cell viability of a sample is defined as the ratio of the number of cells grown on the surface of the sample to the number of cells grown in a control sample (the environment in which cells grow under the best conditions), and if the cell viability is 80% or more, the sample is considered biocompatible.

7A and 7B, four samples, that is, PDMS_40 and a4-PDMS_40 thermally cured at 40° C., PDMS_70 and a4-PDMS_70 thermally cured at 70° C. all have a cell viability of 80% or more, from which Triton x- It can be seen that 100 does not affect the biocompatibility of the polydimethylsiloxane matrix.

The cell viability of a sample is defined as the ratio of the number of cells grown on the sample surface to the number of cells grown in a control sample (the environment in which cells grow under the best conditions), and if the cell viability is 80% or more, the sample is considered biocompatible.

Referring to FIG. 7C, it can be seen that when the addition of Triton x-100 and the thermosetting temperature is lowered, the absorbance is lowered. Absorbance is measured using the CCK-8 kit and is proportional to the rate of cell proliferation because the CCK-8 kit detects signals from living cells.

Therefore, it can be seen that the addition of Triton x-100 and the low heat curing temperature independently induces a decrease in the cell proliferation rate, and in particular, a4-PDMS_40 has a significantly lower cell proliferation rate than other samples. In order for cells to proliferate, the surface must be smooth enough for cells to grow, but a4-PDMS_40 has a low cell proliferation rate due to its high surface roughness.

8 is a graph showing the light transmittance of an adhesive transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention.

Referring to FIG. 8, the adhesive transparent electrode based on the adhesive polydimethylsiloxane matrix containing 0.4% by weight of Triton x-100, which has silver nanowires embedded and heat-cured at 40°C, has surface resistance (R _S ) It can be seen that this is 35 Ω·sq ^-1 and the light transmittance is about 75%.

9A is a graph showing the results of performing an elasticity test to evaluate the elasticity of an adhesive transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention, and FIGS. 9B to 9E are It shows a field emission-scanning electron microscope (FE-SEM, Field Emission-Scanning Electron Microscopy) image before and after stretching.

To perform the elasticity test, samples of a transparent electrode based on a polydimethylsiloxane matrix (PDMS_40NW) and a transparent electrode based on a4-PDMS_40 (a4-PDMS_40NW), an adhesive polydimethylsiloxane matrix, were used, and 500 cycles at a strain rate of 12.5% ).

The a3-PDMS_40-based transparent electrode (a3-PDMS_40NW) sample was used only for the a4-PDMS_40NW sample because the surface resistance was too high to be applied to the transparent electrode.

Referring to FIG. 9A, it can be seen that the ratio (R/R ₀ ) of the surface resistance of a4-PDMS_40NW decreases to 0.8 after 100 cycles and reaches 0.94 after 500 cycles. On the other hand, it can be seen that the ratio of the surface resistance of PDMS_40NW continues to increase and reaches 1.5 after 500 cycles.

Referring to FIG. 9B, it can be observed that the peeling of the silver nanowires is severe even before the periodic elasticity test in the PDMS_40NW. Referring to FIG. 9C, it can be seen that the silver nanowires are broken after a periodic elasticity test (Fig. 9c). Yes (red dotted line). From this, it can be seen that since the adhesion between the polydimethylsiloxane matrix and the silver nanowires is low, the silver nanowires are not well embedded in the polydimethylsiloxane matrix.

On the other hand, referring to FIG. 9D, it can be seen that a4-PDMS_40NW does not show peeling of AgNW, and referring to FIG. 9E, a4-PDMS_40NW did not fracture after a periodic elasticity test. This shows excellence.

Since the PEG chain of Triton x-100 can participate in electrostatic interactions with silver nanowires, the adhesion between a4-PDMS_40 and silver nanowires is higher than that between PDMS_40 and silver nanowires.

Since the adhesion between a4-PDMS_40 and silver nanowires is good, the elasticity of the a4-PDMS_40NW electrode is improved. Another reason why the ratio of surface resistance decreased after stretching 100 times is that the alignment of the silver nanowires changed along the stretching direction. According to previous work by other researchers, silver nanowires can be aligned along the stretch direction during mechanical stretching.

Since the adhesion between the silver nanowire and a4-PDMS_40 is strong due to Triton x-100, the silver nanowire inserted in the a4-PDMS_40 can be aligned along the stretching direction during periodic stretching.

Hereinafter, characteristics when the adhesive transparent electrode based on the adhesive polydimethylsiloxane matrix in which silver nanowires are embedded according to an embodiment of the present invention are applied to a strain sensor and an ECG sensor will be described.

FIG. 10A is a photograph illustrating a case of attaching a deformation sensor to a wrist to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIG. 10B is A picture of a case where a deformation sensor to which a polydimethylsiloxane matrix-based adhesive transparent electrode (PDMS_40NW) is applied is attached to a wrist according to an embodiment of the present invention.

10A and 10B, a4-PDMS_40NW showed a perfectly conformal contact with the skin, and was also shown by repeated bending motions of the wrist 10 times (the third image in FIG. 10A). It can be seen that it does not peel off. However, in PDMS_40NW, it can be seen that the deformation sensor peels off the skin even during the first bending motion (the second image in FIG. 10B).

Figure 10c is a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires and a transparent electrode (PDMS_40NW) based on a polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention. It is a graph showing the relative resistance change of the applied strain sensor.

Referring to FIG. 10C, it can be seen that a4-PDMS_40NW exhibits a greater change in electrical resistance than PDMS_40NW for the same applied strain, and it can be seen that the sensitivity of a4-PDMS_40NW is significantly higher than that of PDMS_40NW in a fixed strain. . This difference is due to the high conformability and elasticity of a4-PDMS_40NW to the skin compared to PDMS_40NW.

In addition, as shown in FIG. 10C, the strain sensor to which a4-PDMS_40NW is applied exhibits low hysteresis, and the relative resistance change (ΔR·R ₀ ^-1 ) is maintained at zero during periodic bending of the wrist.

However, the strain sensor with PDMS_40NW exhibits a high hysteresis characteristic that greatly degrades the performance of the strain sensor, and the ΔR·R ₀ ^-1 ratio in the straight state increases continuously during multiple bending cycles of the wrist.

11A to 11C are an adhesive polydimethylsiloxane matrix-based transparent electrode (a4-PDMS_40NW) embedded with silver nanowires and a polydimethylsiloxane matrix-based adhesive transparent electrode embedded with silver nanowires according to an embodiment of the present invention ( PDMS_40NW) is a photograph of an ECG sensor applied to each arm attached to each arm, and FIG. 11D is a graph showing skin impedance measured using the ECG sensor.

Referring to FIG. 11A, in order to measure skin impedance, an ECG sensor to which a4-PDMS_40NW was applied was attached to the arm at an interval of 3 cm, and it can be seen that the sensor was well attached to the arm without lifting. Also, looking at the image shown below, it can be seen that the sensor is well attached to the arm without lifting when viewed from a different angle.

On the other hand, referring to FIG. 11B, it can be seen that when the ECG sensor to which the PDMS_40NW is applied is attached without an adhesive tape, it is easily peeled off due to poor adhesion to the skin. Therefore, in order to improve the adhesion with the skin, the ECG sensor to which PDMS_40NW was applied was attached using an adhesive tape as shown in FIG. 11C.

Referring to FIG. 11D, in the case of the ECG sensor to which PDMS_40NW is applied, it can be seen that the skin impedance is very high as the adhesion with the skin is poor and the degree of compliance is low.

Therefore, when the ECG sensor to which the PDMS_40NW is applied, which has poor adhesion to the skin, is attached using an adhesive tape, the adhesion to the skin increases, so it can be seen that the skin impedance is lower than when the adhesive tape is not used.

In addition, in the case of an ECG sensor to which a4-PDMS_40NW is applied, it can be seen that the skin impedance is lower than that of the ECG sensor to which PDMS_40NW is applied and an ECG sensor attached using an adhesive tape.

From this, when recording an ECG signal, it can be seen that adhesion with the skin is very important.

FIG. 11E is a photograph illustrating a case where a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is separated from the skin.

Referring to FIG. 11E, it can be seen that no residues remain on the skin even after separating a4-PDMS_40NW from the skin, and it is advantageous when applying the ECG sensor because it does not cause skin irritation or allergic reactions due to residues on the skin. Able to know.

12A is a view showing the electrode position of an ECG sensor to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIGS. 12B to 12E are ECG sensors It is a graph showing the ECG signal measured by.

To measure the ECG signal, a commercial gel, an adhesive transparent electrode based on a polydimethylsiloxane matrix embedded with silver nanowires (PDMS_40NW), and a transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires (a4- PDMS_40NW) was applied to the ECG sensor.

As shown in FIG. 12A, three electrodes were attached to the right side of the chest, the left side of the chest, and the lower right side of the rib cage to measure the electrocardiogram.

Referring to FIGS. 12B and 12C, when compared with the case of using an ECG sensor to which a commercial gel-based transparent electrode is applied as shown in FIG. 12B, some signals in the case of an ECG sensor to which PDMS_40NW is applied as shown in FIG. 12C It can be seen that low signal noise and significant noise are not observed in the P-wave.

Referring to FIG. 12D, in the case of an ECG sensor using an adhesive tape to improve contact between the PDMS_40NW and the skin, the noise of the ECG signal was slightly reduced compared to the ECG sensor to which the PDMS_40NW shown in FIG. 12C was applied, but still signal noise. You can see that there is this.

Referring to FIG. 12E, it can be seen that the ECG sensor to which a4-PDMS_40NW is applied has much less noise of the ECG signal when compared to the ECG sensor to which the commercial gel-based transparent electrode shown in FIG. 12B is applied.

13A to 13D show electrode positions of an ECG sensor to which a transparent electrode (a4-PDMS_40NW) based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires according to an embodiment of the present invention is applied, and FIGS. 13B to 13D Is a graph showing an ECG signal measured by an ECG sensor.

To measure the ECG signal, a commercial gel, an adhesive transparent electrode based on a polydimethylsiloxane matrix embedded with silver nanowires (PDMS_40NW), and a transparent electrode based on an adhesive polydimethylsiloxane matrix embedded with silver nanowires (a4- PDMS_40NW) was applied to the ECG sensor.

In addition, in the case of the ECG sensor to which PDMS_40NW was applied, an attachment tape was used to improve contact with the skin.

As shown in FIG. 13A, three electrodes were attached to both arms and left ankles to measure ECG.

13B to 13D, due to the distance between the electrode and the heart, it can be seen that the noise of the ECG signal is larger than that when the ECG sensor is attached to the chest (see FIGS. 12B to 12E).

13C, the ECG sensor to which the PDMS_40NW was applied, despite the use of a contact tape to improve the contact force with the skin, showed very severe noise of the ECG signal, which indicates that the contact with the arm skin is very weak. I can.

Referring to FIG. 13D, it can be seen that the ECG sensor to which a4-PDMS_40NW is applied shows a clear and stable ECG signal similar to the ECG sensor to which a commercial gel-based transparent electrode is applied.

In the case of the ECG sensor with a4-PDMS_40NW applied, it can be seen that the signal noise is low due to the high compliance with the skin and the high electrical conductivity of the embedded silver nanowire.

It can be seen that the ECG sensor applied with a4-PDMS_40NW has higher adhesion to the skin than the ECG sensor applied with PDMS_40NW, and has significantly improved biocompatibility compared to the ECG sensor applied with a commercial gel-based transparent electrode.

As described above, it can be seen that a transparent electrode in which a silver nanowire network is embedded in an adhesive polydimethylsiloxane matrix containing a nonionic surfactant has very high compliance for application as a skin biosensor.

It can be seen that the conformability of the electrode is improved by improving mechanical properties such as adhesion, compliance, and viscoelasticity of the tacky polydimethylsiloxane matrix.

The mechanical properties as described above are due to the interaction of the platinum (Pt) catalyst present in the polydimethylsiloxane curing agent and the polar functional groups present in Triton x-100 by controlling the curing temperature and adding Triton x-100, a nonionic surfactant. It can be improved as the crosslinking reaction of polydimethylsiloxane is hindered.

In addition, in the case of the sensor to which the transparent electrode according to the present invention is applied, the detection sensitivity of various biological signals such as EMG, EEG and glucose can be greatly improved. It can be used as an electrode material for various wearable electronic devices such as.

As described above, although the present invention has been described by limited embodiments and drawings, the present invention is not limited to the above embodiments, and various modifications and variations from the above description are provided for those of ordinary skill in the art to which the present invention pertains. Transformation is possible. Therefore, the scope of the present invention is limited to the described embodiments and should not be defined, but should be defined by the claims to be described later as well as equivalents to the claims.

Claims (9)

Board; And
A silver (Ag) nanowire network deposited on the substrate includes an embedded adhesive polydimethylsiloxane (PDMS) matrix,
The tacky polydimethylsiloxane matrix comprises a polydimethylsiloxane including a polydimethylsiloxane base and a polydimethylsiloxane curing agent and a nonionic surfactant,
The tacky polydimethylsiloxane matrix is composed of crosslinked and non-crosslinked polydimethylsiloxane by the nonionic surfactant, and is heterogeneously crosslinked,
The tacky polydimethylsiloxane matrix,
The dispersion liquid is coated on the substrate coated with the silver nanowire network at 3 rpm to 400 rpm for 15 seconds to 30 seconds through spin coating and then thermally cured at 40° C. to 50° C. for 9 hours to 11 hours. ,
The dispersion contains 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol as the polydimethylsiloxane base, the polydimethylsiloxane curing agent, and the nonionic surfactant from 10:1:0.03 to 10:1 : It is prepared by mixing at a weight ratio of 0.05, wherein the polydimethylsiloxane base material and the polydimethylsiloxane curing agent are fixed at a ratio of 10:1. The method of claim 1,
Due to the interaction of the platinum (Pt) catalyst present in the polydimethylsiloxane curing agent and the polar functional group present in the nonionic surfactant, the crosslinking reaction of the polydimethylsiloxane is hindered, and the adhesive poly Adhesive transparent electrode, characterized in that the mechanical properties of the dimethylsiloxane matrix are improved. The method of claim 1,
An adhesive transparent electrode, characterized in that the silver nanowire network is embedded in the adhesive polydimethylsiloxane matrix due to the interaction between the polar functional group present in the nonionic surfactant and the polar functional group present in the silver nanowire network. The method of claim 1,
The nonionic surfactant is 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol, fatty alcohol-polyoxyethylene ether, polyoxyethylene sorbitan fatty acid ester (polyoxyethylene). sorbitan fatty acid esters), polyoxyethylene faty acid ester, polyoxyethylene alkylether, sorbitan esters, glyceryl esters, glyceryl monostearate monostearate), polyethylene glycol, polypropylene glycol, polypropylene glycol esters, cetyl alcohol, cetostearyl alcohol, stearyl alcohol ) At least one of the adhesive transparent electrode, characterized in that. The method of claim 1,
The nonionic surfactant is an adhesive transparent electrode, characterized in that it has a weight ratio of 0.3% to 0.4% by weight. Forming a silver nanowire network on the substrate;
Coating a dispersion comprising a polydimethylsiloxane base material, a polydimethylsiloxane curing agent, and a nonionic surfactant on the substrate on which the silver nanowire network is formed; And
Forming an adhesive polydimethylsiloxane matrix in which the silver nanowire network is embedded by thermally curing the dispersion solution coated on the substrate on which the silver nanowire network is formed
Including,
The adhesive polydimethylsiloxane matrix is composed of crosslinked and non-crosslinked polydimethylsiloxane by the nonionic surfactant, and is heterogeneously crosslinked,
The dispersion liquid is coated on the substrate coated with the silver nanowire network at 3 rpm to 400 rpm for 15 seconds to 30 seconds through spin coating and then thermally cured at 40° C. to 50° C. for 9 hours to 11 hours. ,
The dispersion contains 4-(1,1,3,3-tetramethylbutyl)phenyl-polyethylene glycol as the polydimethylsiloxane base, the polydimethylsiloxane curing agent, and the nonionic surfactant from 10:1:0.03 to 10:1 : It is prepared by mixing at a weight ratio of 0.05, the polydimethylsiloxane main body, the polydimethylsiloxane curing agent is fixed at a ratio of 10:1. The method of claim 6,
The method of manufacturing an adhesive transparent electrode, further comprising the step of separating the adhesive polydimethylsiloxane matrix in which the silver nanowire network is embedded from the substrate. The method of claim 6,
The step of forming a nanowire network on the substrate
Coating a silver nanowire solution on the substrate; And
And annealing the substrate coated with the silver nanowire solution. The method of claim 8,
The method of manufacturing an adhesive transparent electrode, characterized in that the substrate coated with the silver nanowire solution is annealed at 100° C. to 180° C. for 5 to 20 minutes.

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