A medical skin adhesive and its preparation method

Abstract

This invention discloses a method for preparing a medical skin adhesive, comprising the following steps: S1: Modifying bioactive glass using acryloyloxypropyltrioxysilane; S2: Mixing it with a graphene oxide dispersion and adding a crosslinking agent to obtain a prepolymer; S3: Adding ethyl methyl imidazolium phosphate dihydrogen salt for low-field treatment, then adding an absorbable material for high-field treatment, and heating the reaction to obtain a modified A-O hydrogel with a micro / nano structure; S4: Encapsulating active ingredients in an adhesive matrix using a spray-drying method to obtain a sustained-release carrier; S5: Compounding the modified A-O hydrogel and the sustained-release carrier with cyanoacrylate and additives to obtain the medical skin adhesive. This preparation method not only improves the adhesive's adhesion performance in humid environments but also significantly promotes wound healing, meeting the clinical application requirements for high efficiency, safety, and multifunctionality.

Description

Technical Field

[0001] This invention relates to the technical field of adhesives, and more particularly to a medical skin adhesive and its preparation method. Background Technology

[0002] Medical skin adhesives are medical glues used for closing and repairing skin wounds, and are widely used in clinical treatment. Compared with traditional suture methods, medical skin adhesives have advantages such as reducing pain and the incidence of inflammation, while also reducing scar formation and improving the aesthetics of the postoperative wound. Furthermore, the use of medical skin adhesives eliminates the need for suture removal, simplifying the postoperative care process, and is especially suitable for children and young female patients.

[0003] However, existing medical skin adhesives still have some shortcomings in practical applications. For example, many adhesives exhibit poor adhesion in wet environments (such as wound exudate or moist skin surfaces), easily leading to adhesive failure. Furthermore, some adhesives lack long-lasting hemostatic, antibacterial, and wound-healing-promoting functions, increasing the risk of wound infection and prolonging healing time. These problems limit the effectiveness and scope of medical skin adhesives in clinical applications. Therefore, developing a medical skin adhesive that maintains excellent adhesion in wet environments and provides long-lasting hemostatic, antibacterial, and wound-healing-promoting effects is an important current research direction. Summary of the Invention

[0004] In view of the shortcomings of the prior art, the present invention provides a method for preparing a medical skin adhesive to solve the technical problems of insufficient adhesion performance of traditional medical skin adhesives in wet environments, as well as the lack of long-lasting hemostatic, antibacterial and wound-healing functions.

[0005] To achieve the above objectives, the technical solution adopted by the present invention is as follows:

[0006] A method for preparing a medical skin adhesive, the method comprising the following steps:

[0007] S1: The bioactive glass is placed in an ethanol-water solution of acryloyloxypropyltrioxysilane, and after reacting with an alkaline solution, it is subjected to high-temperature heat treatment to obtain modified bioactive glass. In step S1 of this application, the modification of bioactive glass is achieved by utilizing the dual active functional group characteristics of acryloyloxypropyltrioxysilane. The trioxysilane group can undergo a condensation reaction with the hydroxyl groups on the surface of the bioactive glass after hydrolysis to form a stable chemical bond, while the acryloyloxy group provides an active site for the subsequent polymerization reaction. This modification process not only enhances the dispersibility and binding ability of bioactive glass in skin adhesives, but also helps the bioactive glass to better interact with skin tissue in a humid environment, promoting cell adhesion and tissue repair.

[0008] S2: Mix the modified bioactive glass obtained in step S1 with the graphene oxide dispersion, add an appropriate amount of crosslinking agent, stir evenly, and obtain a prepolymer solution.

[0009] S3: Add ethyl methyl imidazolium phosphate dihydrogen ionic liquid to the prepolymer obtained in step S2, stir evenly, and then treat it in a low electric field. Then add absorbable material, mix evenly, pour into a mold with a high electric field, heat to react, and finally soak and rinse with deionized water to obtain a modified AO hydrogel with micro-nano structure. The modified AO hydrogel with micro-nano structure prepared by this invention, on the one hand, through the reaction of modified bioactive glass with graphene oxide dispersion and hydrophobic crosslinking agent, a network structure formed by the reaction of modified bioactive glass and crosslinking agent is coated on the surface of graphene oxide, which effectively balances the hydrophilicity and hydrophobicity of the system, prevents the adhesive from excessive swelling in a humid environment, and ensures its long-term adhesion. It maintains good adhesion properties even when in contact with water. On the other hand, by combining low-field and high-field treatment with the introduction of ethyl methyl imidazolium dihydrogen phosphate ionic liquid, not only was the gradient distribution of the hydrogel's micro-nano pore structure regulated, enhancing its stability and mechanical properties in a humid environment, but it also promoted cell adhesion and tissue repair. Furthermore, it further promoted the synergistic effect between bioactive glass and graphene oxide. Specifically, bioactive glass provides essential minerals for skin cell proliferation and migration by releasing calcium and phosphorus ions, accelerating wound healing, while the high thermal conductivity of graphene oxide helps regulate the local temperature of the wound, creating a more suitable environment for wound healing and promoting the release of calcium and phosphorus ions from the bioactive glass.

[0010] S4: The active ingredient is encapsulated in the adhesive matrix using a spray-drying method to obtain a sustained-release carrier. The sustained-release carrier obtained in step S4 not only achieves efficient loading and uniform distribution of the active ingredient, but also effectively controls the release rate of the active ingredient, enabling it to continuously exert its effects during adhesive use, such as promoting wound healing, antibacterial activity, and hemostasis. This sustained-release design significantly enhances the biocompatibility and therapeutic efficacy of the adhesive, while reducing potential side effects caused by premature release or excessively high concentrations of the active ingredient.

[0011] S5: The modified AO hydrogel obtained in step S3 and the sustained-release carrier obtained in step S4 are compounded with cyanoacrylate and additives. After mixing and stirring evenly, the mixture is dried to obtain the medical skin adhesive. In step S5 of this application, the compounding of cyanoacrylate and additives further optimizes the overall performance of the medical skin adhesive. Cyanoacrylate has rapid curing and strong adhesion properties. It works synergistically with the modified AO hydrogel to form a more stable adhesive system, significantly enhancing the adhesive strength and stability, enabling it to quickly and firmly bond wounds. The addition of additives improves the adhesive's moisturizing, anti-corrosion, and antioxidant properties, making it more stable and reliable during use, and better meeting the needs of use under different environments and conditions. In addition, the compounded medical skin adhesive has good fluidity and operability, making it easy to apply to the wound surface and quickly cure to form a uniform adhesive film layer, improving the convenience and efficiency of use and solving the problems of insufficient overall performance and inconvenience of use of traditional adhesives.

[0012] As a preferred technical solution, the acryloyloxypropyltrioxysilane is at least one of (3-acryloyloxypropyl)trimethoxysilane, 3-(methacryloyloxy)propyltrimethoxysilane, 3-acryloyloxypropyltriethoxysilane, and methacryloyloxypropyltriethoxysilane.

[0013] As a preferred technical solution, the crosslinking agent is composed of isoprene and a di-imidazolium salt ionic liquid. By introducing a di-imidazolium salt ionic liquid, the crosslinking agent of this application, due to its unique ionic properties, hydrophobicity, and the reactivity of its unsaturated double bonds, can not only undergo a highly efficient crosslinking reaction with bioactive glass to form a stable network structure, significantly enhancing the mechanical properties and stability of the adhesive in humid environments, but also effectively balances the hydrophilicity and hydrophobicity of the system, preventing excessive swelling of the adhesive in humid environments and ensuring that it maintains good adhesion performance even after prolonged contact with moisture.

[0014] As a preferred technical solution, the preparation method of the binary imidazolium salt ionic liquid is as follows: 1-allyl-5-vinyl-1H-imidazolium and bromoalkane are mixed in a suitable solvent, an appropriate amount of alkali is added, the reaction temperature is controlled at 60-80℃, and the reaction time is 6-12 hours to obtain the binary imidazolium salt ionic liquid.

[0015] As a preferred technical solution, the electric field strength of the low electric field is 1-5 kV / cm, and the electric field strength of the high electric field is 5-10 kV / cm.

[0016] As a preferred technical solution, the absorbable material is at least one of fibroin, keratin, collagen, proteoglycan, gelatin, and lactic acid polymer.

[0017] As a preferred technical solution, the active factor is at least one of epidermal growth factor, coagulation factor, and antibacterial agent.

[0018] As a preferred technical solution, the adhesive matrix is ​​composed of chitosan and gelatin.

[0019] As a preferred technical solution, the cyanoacrylate is octyl α-cyanoacrylate and / or isooctyl α-cyanoacrylate.

[0020] As a preferred technical solution, the additive is at least one of humectant, preservative, antioxidant, lubricant, and defoamer.

[0021] Another aspect of the present invention is to provide a medical skin adhesive, which is prepared by the method described above for preparing a medical skin adhesive.

[0022] The beneficial effects of this invention are:

[0023] This invention discloses a method for preparing a medical skin adhesive. Through innovative modification of a bioactive glass surface using acryloyloxypropyltrioxysilane, combined with the synergistic effects of graphene oxide, ethylmethylimidazolium dihydrogen phosphate ionic liquid, and absorbable materials, and by optimizing the micro / nano structure of the hydrogel using both low and high electric field treatments, the adhesive achieves excellent adhesion and stability in wet environments, and significantly promotes wound healing. This design not only enhances the adhesive's mechanical properties and biocompatibility but also maintains its long-lasting adhesion to moist skin surfaces, helping to accelerate wound healing and reduce the risk of infection.

[0024] In summary, the medical skin adhesive of the present invention not only possesses excellent adhesion strength and biocompatibility, but also exhibits good properties in promoting epidermal growth, antibacterial activity, hemostasis, and wound healing. It can meet the high performance requirements of medical skin adhesives in wet environments, providing a more efficient and safer solution for clinical wound care. Detailed Implementation

[0025] The following description is intended to disclose the invention and enable those skilled in the art to implement it. The preferred embodiments described below are merely examples, and other obvious variations will occur to those skilled in the art. Example 1

[0026] The preparation method of the medical skin adhesive in this embodiment includes the following steps:

[0027] S1: 16g of bioactive glass was placed in 100mL of an ethanol-water solution of (3-acryloyloxypropyl)trimethoxysilane (ethanol and deionized water volume ratio of 1:1), the mass concentration of which was 50g / L. 15mL of 0.5mol / L sodium hydroxide solution was added and reacted for 30min. After that, it was heat-treated at 110℃ for 2 hours. After cooling to room temperature, it was washed repeatedly with ethanol solution 3 times, centrifuged for 5min each time. Finally, it was heat-treated in an oven at 80℃ for 1 hour to obtain modified bioactive glass.

[0028] S2: The modified bioactive glass obtained in step S1 is mixed with 140 mL of graphene oxide dispersion with a concentration of 10 mg / mL (the dispersant is composed of ethanol and deionized water in a volume ratio of 2:1, the same below), and 7.7 g of crosslinking agent (composed of isoprene and diene imidazole salt ionic liquid in a mass ratio of 2:5) is added. The mixture is stirred evenly with ultrasonic assistance at 60 °C for 20 min to obtain the prepolymer solution.

[0029] S3: Add 8g of ethyl methyl imidazolium dihydrogen phosphate ionic liquid to the prepolymer obtained in step S2, stir evenly, and then treat it in a low electric field (electric field strength of 2kV / cm) for 2 hours. Then add 90g of absorbable material gelatin, mix evenly, and pour it into a mold with a high electric field (electric field strength of 6kV / cm). React at 80℃ for 8 hours, and then soak it in deionized water. Rinse repeatedly 3 times, soaking for 8 hours each time to remove residual ionic liquid, and finally obtain modified AO hydrogel with micro-nano structure.

[0030] S4: Epidermal growth factor (EGF), coagulation factor (thrombin), and antimicrobial agent (antimicrobial peptide) are used as active factors and encapsulated in an adhesive matrix (composed of chitosan and gelatin) by spray drying to obtain a sustained-release carrier. The specific steps are as follows: Epidermal growth factor (EGF), coagulation factor (thrombin), and antimicrobial agent (antimicrobial peptide) are dissolved in deionized water at a mass ratio of 1:2:2 to prepare an active factor solution. Chitosan and gelatin are mixed and dissolved in acetic acid solution at a mass ratio of 1:1, stirred evenly, and then mixed with the active factor solution at a volume ratio of 1:4 to obtain a spray-drying precursor solution. The precursor solution is loaded into the injector of the spray drying device, the inlet air temperature is set to 150℃, the flow rate is 1.5 mL / min, and microspheres with a diameter of approximately 10-50 µm are obtained through spray drying. The microspheres were soaked in deionized water for 1 hour to remove impurities, rinsed repeatedly with deionized water 3 times for 15 minutes each time, and finally dried at 40°C for 2 hours to obtain sustained-release carrier microspheres loaded with active factors.

[0031] S5: 48g of the modified AO hydrogel obtained in step S3 and 6g of the sustained-release carrier obtained in step S4 are compounded with 16g of octyl α-cyanoacrylate and 12g of additives. After mixing and stirring evenly, the mixture is dried to obtain the medical skin adhesive. The additives consist of 4g of hyaluronic acid (moisturizer), 3g of phenoxyethanol (preservative), 2g of ascorbic acid (antioxidant), 2g of magnesium stearate (lubricant), and 1g of polydimethylsiloxane (defoamer).

[0032] The preparation method of the binary imidazolium salt ionic liquid is as follows: 13.4g of 1-allyl-5-vinyl-1H-imidazolium and 15g of bromoethane are mixed in 100mL of ethanol solvent, 5g of sodium hydroxide is added as a base, the reaction temperature is controlled at 60℃, and the reaction time is 8 hours to obtain the binary imidazolium salt ionic liquid. Example 2

[0033] The preparation method of the medical skin adhesive in this embodiment includes the following steps:

[0034] S1: 18g of bioactive glass was placed in 100mL of an ethanol-water solution of 3-(methacryloyloxy)propyltrimethoxysilane (ethanol and deionized water volume ratio of 1:1), the mass concentration of which was 60g / L. 20mL of 0.5mol / L sodium hydroxide solution was added and reacted for 30min. After that, it was subjected to high-temperature heat treatment at 120℃ for 2 hours. After cooling to room temperature, it was repeatedly washed 3 times with ethanol solution, centrifuged for 5 minutes each time. Finally, it was heat-treated in an oven at 80℃ for 1 hour to obtain modified bioactive glass.

[0035] S2: The modified bioactive glass obtained in step S1 was mixed with 150 mL of graphene oxide dispersion with a concentration of 10 mg / mL, and 8.8 g of crosslinking agent (composed of isoprene and diene imidazole salt ionic liquid in a mass ratio of 1:3) was added. The mixture was stirred evenly with ultrasonic assistance at 60 °C for 15 min to obtain a prepolymer solution. The diene imidazole salt ionic liquid is the same as in Example 1.

[0036] S3: Add 10g of ethyl methyl imidazolium dihydrogen phosphate ionic liquid to the prepolymer obtained in step S2, stir evenly, and then treat it in a low electric field (electric field strength of 3kV / cm) for 2 hours. Then add 100g of absorbable material gelatin, mix evenly, and pour it into a mold with a high electric field (electric field strength of 7kV / cm). React at 80℃ for 8 hours, and then soak it in deionized water. Rinse repeatedly 3 times, soaking for 8 hours each time, to remove residual ionic liquid, and finally obtain modified AO hydrogel with micro-nano structure.

[0037] S4: Epidermal growth factor (EGF), coagulation factor (thrombin), and antibacterial agent (antimicrobial peptide) are used as active factors and encapsulated in an adhesive matrix (composed of chitosan and gelatin) by spray drying to obtain a sustained-release carrier. The specific operation steps are the same as in Example 1.

[0038] S5: 50g of the modified AO hydrogel obtained in step S3 and 8g of the sustained-release carrier obtained in step S4 are compounded with 18g of isooctyl α-cyanoacrylate and 12g of additives. After mixing and stirring evenly, the mixture is dried to obtain the medical skin adhesive. The additives are the same as in Example 1. Example 3

[0039] The preparation method of the medical skin adhesive in this embodiment includes the following steps:

[0040] S1: Place 20g of bioactive glass in 100mL of an ethanol-water solution of 3-acryloyloxypropyltriethoxysilane (ethanol to deionized water volume ratio of 1:1), wherein the mass concentration of 3-acryloyloxypropyltriethoxysilane is 70g / L. Add 25mL of 0.5mol / L sodium hydroxide solution and react for 30min. Then, heat treat at 120℃ for 2 hours. After cooling to room temperature, wash repeatedly with ethanol solution 3 times, centrifuge for 5min each time. Finally, heat treat in an oven at 80℃ for 1 hour to obtain modified bioactive glass.

[0041] S2: The modified bioactive glass obtained in step S1 was mixed with 160 mL of graphene oxide dispersion with a concentration of 10 mg / mL, and 10.2 g of crosslinking agent (composed of isoprene and diene imidazole salt ionic liquid in a mass ratio of 1:2) was added. The mixture was stirred evenly with ultrasonic assistance at 60 °C for 15 min to obtain a prepolymer solution. The diene imidazole salt ionic liquid is the same as in Example 1.

[0042] S3: Add 12g of ethyl methyl imidazolium dihydrogen phosphate ionic liquid to the prepolymer obtained in step S2, stir evenly, and then treat it in a low electric field (electric field strength of 4kV / cm) for 2 hours. Then add 110g of absorbable material gelatin, mix evenly, and pour it into a mold with a high electric field (electric field strength of 8kV / cm). React at 80℃ for 8 hours, and then soak it in deionized water. Rinse it repeatedly 3 times, soaking for 8 hours each time to remove residual ionic liquid, and finally obtain modified AO hydrogel with micro-nano structure.

[0043] S4: Epidermal growth factor (EGF), coagulation factor (thrombin), and antibacterial agent (antimicrobial peptide) are used as active factors and encapsulated in an adhesive matrix (composed of chitosan and gelatin) by spray drying to obtain a sustained-release carrier. The specific operation steps are the same as in Example 1.

[0044] S5: 52g of the modified AO hydrogel obtained in step S3 and 10g of the sustained-release carrier obtained in step S4 are compounded with 18g of octyl α-cyanoacrylate and 12g of additives. After mixing and stirring evenly, the mixture is dried to obtain the medical skin adhesive. The additives are the same as in Example 1.

[0045] Comparative Example 1

[0046] The preparation method of this comparative example of medical skin adhesive is basically the same as that of Example 1 in terms of raw material composition and preparation steps. The difference is that step S1 is not performed in the preparation method of this comparative example.

[0047] Comparative Example 2

[0048] The preparation method of this comparative example of medical skin adhesive is basically the same as that of Example 1 in terms of raw material composition and preparation steps. The difference is that step S2 is not performed in the preparation method of this comparative example.

[0049] Comparative Example 3

[0050] The preparation method of this comparative example of medical skin adhesive is basically the same as that of Example 1 in terms of raw material composition and preparation steps. The difference is that in the preparation method of this comparative example, step S3 is not subjected to low electric field and high electric field treatment.

[0051] The medical skin adhesives prepared in Examples 1-3 and Comparative Examples 1-3 were subjected to performance tests, and the performance results are shown in Table 1:

[0052] The adhesive strength test method is as follows: First, medical skin adhesive is evenly applied to a standard test plate to form an adhesive layer of uniform thickness (0.5 mm ± 0.1 mm), and cured for 24 hours at 25°C and 50% relative humidity. Then, using a universal testing machine, the test plate is fixed in a fixture, and a tensile test is performed at a tensile speed of 10 mm / min, recording the maximum tensile force. Finally, the result is calculated using the formula: "Adhesive strength (MPa) = Maximum tensile force (N) / Adhesive area (m²)".

[0053] The test method for adhesive strength under wet conditions is as follows: Medical skin adhesive is evenly applied to a standard test plate to form an adhesive layer of uniform thickness (0.5 mm ± 0.1 mm), and cured for 24 hours at 25℃ and 50% relative humidity. After curing, the sample is immersed in deionized water for 24 hours to simulate a wet environment. After immersion, the surface moisture is absorbed with filter paper, and the sample is fixed in the fixture of a universal testing machine. The test is conducted at a tensile speed of 10 mm / min, and the maximum tensile force (N) is recorded. The adhesive area (m²) is measured, and the result is calculated using the formula "Adhesive strength (MPa @ wet environment) = Maximum tensile force (N) / Adhesive area (m²)".

[0054] The biocompatibility testing method was as follows: Medical skin adhesive samples were prepared to standard size and tested using the L929 cell line in DMEM culture medium supplemented with 10% fetal bovine serum. After co-culturing the samples and cells for 24 hours, cell viability was assessed using the MTT assay kit, and cell survival rate was calculated. The cytotoxicity assessment criteria were: cell viability ≥80% was considered non-cytotoxic, 60%–80% was considered mild cytotoxic, and <60% was considered significant cytotoxic.

[0055] The antibacterial test method is as follows: Prepare standard-sized samples (1cm × 1cm × 0.5cm) using medical skin adhesive, and use Staphylococcus aureus (ATCC 6538) or Escherichia coli (ATCC 8739) as the culture medium, which is nutrient broth. Mix the sample with a bacterial suspension (1×10⁻⁶). 6 After co-culturing for 24 hours with samples containing CFU / mL, the viable bacterial count was calculated using the plate count method to determine the inhibition rate. The inhibition rate was calculated using the formula: "Inhibition rate = (Viable bacterial count in control group - Viable bacterial count in experimental group) / Viable bacterial count in control group × 100%". The control group was a blank sample without added medical skin adhesive.

[0056] The method for testing wound healing ability is as follows: medical skin adhesive is applied to the skin wound of an animal model (rat), with a wound area of ​​1 cm². After 7 days, the wound healing is observed, the change in wound area is measured, and the healing rate is calculated.

[0057] Criteria for assessing healing time:

[0058] Complete healing: defined as the wound area being reduced to less than 10% of the initial area, with no obvious exudate, redness, or other inflammatory reactions on the wound surface.

[0059] Partial healing: defined as a reduction in wound area to 30%–10% of the initial area, but still with a certain degree of inflammatory response.

[0060] Unhealed: The wound area is reduced to less than 30% of the initial area, and there is a significant inflammatory response.

[0061] The hemostatic performance was tested as follows: Medical skin adhesive was applied to a skin wound of an animal model (rat), with a wound area of ​​1 cm² and a wound depth of 2 mm. The bleeding time (from wound formation to bleeding cessation) was recorded using a stopwatch, and the average hemostasis time was calculated.

[0062] Table 1

[0063]

[0064] The foregoing has shown and described the basic principles, main features, and advantages of the present invention. Those skilled in the art should understand that the present invention is not limited to the above embodiments. The embodiments and descriptions in the specification are merely principles of the invention. Various changes and modifications can be made to the invention without departing from its spirit and scope, and all such changes and modifications fall within the scope of the claimed invention.

Claims

1. A method for preparing a medical skin adhesive, characterized by, The preparation method comprises the following steps: S1: placing a bioactive glass in an ethanol aqueous solution of acryloxypropyltrioxysilane, adding an alkali solution, and then performing high-temperature heat treatment to obtain a modified bioactive glass; S2: mixing the modified bioactive glass obtained in step S1 with a graphene oxide dispersion liquid, and adding an appropriate amount of a crosslinking agent, and stirring uniformly to obtain a prepolymer liquid; S3: adding ethylmethylimidazolium dihydrogen phosphate ionic liquid to the prepolymer liquid obtained in step S2, stirring uniformly, and then placing in a low electric field for treatment, and then adding an absorbable material, stirring uniformly, and then pouring into a mold with a high electric field, heating and reacting, and finally soaking and washing with deionized water to obtain a modified A-O hydrogel with a micro-nano structure; S4: embedding active factors in an adhesive matrix by a spray drying method to obtain a sustained-release carrier; S5: compounding the modified A-O hydrogel obtained in step S3 and the sustained-release carrier obtained in step S4 with cyanoacrylate and an auxiliary agent, stirring uniformly, and then performing drying treatment to finally obtain the medical skin adhesive. The crosslinking agent is composed of isoprene and a binary olefin imidazole salt ionic liquid; the preparation method of the binary olefin imidazole salt ionic liquid is: mixing 1-allyl-5-vinyl-1H-imidazole and bromoalkane in a proper solvent, adding an appropriate amount of alkali, controlling the reaction temperature to be 60-80 DEG C, and controlling the reaction time to be 6-12 hours to obtain the binary olefin imidazole salt ionic liquid; the electric field intensity of the low electric field is 1-5 kV / cm, and the electric field intensity of the high electric field is 5-10 kV / cm; the absorbable material is at least one of fibrin, keratin, collagen, proteoglycan, gelatin, and lactic acid polymer.

2. The method of preparing a medical skin adhesive as claimed in claim 1, wherein, The acryloxypropyltrioxysilane is at least one of (3-acryloxypropyl)trimethoxysilane, 3-(methacryloxy)propyltrimethoxysilane, 3-acryloxypropyltriethoxysilane, and methacryloxypropyltriethoxysilane.

3. The method of claim 1, wherein the medical skin adhesive is prepared by the steps of: The active factors are at least one of epidermal growth factor, coagulation factor, and antibacterial agent.

4. The method for preparing the medical skin adhesive as described in claim 1, characterized in that, The cyanoacrylate is alpha-cyanoacrylic acid octyl ester and / or alpha-cyanoacrylic acid iso-octyl ester.

5. The method for preparing the medical skin adhesive as described in claim 1, characterized in that, The auxiliary agent is at least one of a moisturizing agent, a preservative, an antioxidant, a lubricant, and an antifoaming agent.

6. A medical skin adhesive characterized by, The adhesive is prepared by the preparation method of the medical skin adhesive according to any one of claims 1-5.

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