An injectable polysiloxane / hyaluronic acid double network hydrogel, its preparation method and postoperative anti-adhesion application

Abstract

This invention belongs to the field of biomedical polymer materials. Specifically, it relates to an injectable dual-network hydrogel, its preparation method, and its application in long-term prevention of postoperative tissue adhesion. The hydrogel consists of two interpenetrating three-dimensional cross-linked networks: one is a polysiloxane network formed by the condensation polymerization of γ-aminopropyltrialkoxysilane; the other is a hyaluronic acid network formed by the cross-linking of thiolized hyaluronic acid through dissolved oxygen oxidation under the catalysis of amino groups in the polysiloxane network. The two networks interpenetrate to form a stable three-dimensional cross-linked structure. Compared with existing anti-adhesion materials that struggle to balance biocompatibility, wet tissue adhesion, and long-term stability, the hydrogel of this invention exhibits good biocompatibility, wet tissue adhesion performance, a slow degradation rate, and injectability. It can be used as a medical barrier material for the prevention of postoperative tissue adhesion, especially suitable for long-term anti-adhesion applications after abdominal and pelvic surgeries.

Description

Technical Field

[0001] This invention relates to the field of biomedical polymer materials technology, and in particular to an injectable polysiloxane / hyaluronic acid dual-network hydrogel, its preparation method, and its postoperative anti-adhesion application. Background Technology

[0002] Tissue adhesions refer to the abnormal fibrous connections that form between adjacent tissues and organs after surgery or trauma. It is a common postoperative complication that can lead to chronic pain, intestinal obstruction, infertility, and other problems, increasing patient suffering and the medical burden (Bioact. Mater. 2023, 26, 387-412). The mechanisms of tissue adhesions are complex, typically involving postoperative local bleeding, coagulation reactions, inflammatory reactions, an imbalance between fibrin deposition and dissolution, fibroblast proliferation, and collagen deposition, usually lasting for weeks or even months (Nat. Commun. 2020, 11(1), 4061). Once significant adhesions form, a second surgery is often required for separation, which not only increases trauma and medical costs but may also trigger new adhesions, creating a vicious cycle (Lancet 2020, 395(10217), 33-41).

[0003] To reduce adhesion, one of the more common strategies is to use physical barrier materials to form an isolation layer on the surface of damaged tissue, preventing adhesion of adjacent tissues during the repair window. An ideal anti-adhesion barrier material should meet the following requirements: (1) good biocompatibility and tissue compatibility; (2) efficient wet tissue adhesion performance; (3) a suitable degradation rate that can cover the critical window period for adhesion formation; and (4) adaptability to irregular wound surfaces and ease of operation under minimally invasive surgical conditions. However, currently available anti-adhesion products such as Seprafilm®, Interceed®, and SurgiWrap® are mostly used in the form of pre-made films or sheets, which have some limitations in actual clinical applications (Acta Biomater. 2025, 204, 76-108). For example, some materials degrade too quickly in vivo, making it difficult to provide an effective barrier during the critical period of adhesion formation; some membrane materials have insufficient adhesion to wet tissue surfaces, which may require additional suturing and fixation, increasing the complexity of the operation and potentially causing new tissue damage; in addition, prefabricated membranes have limited adaptability to irregular, deep or narrow wounds, making it difficult to spread smoothly under minimally invasive conditions, thus affecting their clinical efficacy.

[0004] In recent years, injectable hydrogels have attracted attention due to their ability to form gels in situ, fill irregular defects, and be suitable for minimally invasive procedures. However, injectable hydrogels still generally face the challenge of balancing stability / durability with biocompatibility / operability: on the one hand, if the cross-linking density is insufficient, the hydrogel is prone to rapid swelling or degradation in the body fluid environment, making it difficult to provide a sufficiently long-lasting barrier effect; on the other hand, to obtain higher stability, some systems require the introduction of strong cross-linking agents, oxidants, etc., which may bring potential irritation or residue risks (Adv. Healthcare Mater. 2023, 12(28),2301379). Therefore, developing an anti-adhesion material that can adhere strongly to wet tissue, maintain a stable barrier effect during the critical repair window, and has good biocompatibility and is injectable still has important research and application value.

[0005] Based on the above requirements, this invention proposes an injectable polysiloxane / hyaluronic acid dual-network hydrogel and its preparation method. This hydrogel combines a polysiloxane network and a mercapto-modified hyaluronic acid network. Through their interpenetration and synergistic effect, the hydrogel's structural stability, wet tissue adhesion properties, and long-term anti-adhesion capability are effectively improved. The main characteristics of this dual-network hydrogel are: 1. The polysiloxane network, formed from γ-aminopropyltrialkoxysilane via hydrolysis and condensation, provides high mechanical strength and long-term stability; 2. The mercapto-modified hyaluronic acid, catalyzed by the amino groups of the polysiloxane network, undergoes dissolved oxygen oxidation to form disulfide bonds, thus achieving in-situ cross-linking without the introduction of exogenous oxidants; 3. The dual-network structure has a slow degradation rate, maintaining stability during the critical window period for adhesion formation and preventing postoperative tissue adhesion. This hydrogel can be used as a medical barrier material for postoperative tissue adhesion prevention, especially suitable for long-term anti-adhesion applications after abdominal and pelvic surgeries. Summary of the Invention

[0006] In view of this, the technical problem to be solved by the present invention is to provide a hydrogel with a simple preparation process and a rapid gelation at room temperature, and the preparation method thereof, so as to solve the problem that existing anti-adhesion materials are difficult to balance wet tissue adhesion, long-term stability and biosafety.

[0007] To achieve the above objectives, the technical solution of the present invention is as follows:

[0008] In a first aspect, the present invention provides an injectable polysiloxane / hyaluronic acid dual-network hydrogel, the hydrogel comprising:

[0009] (a) A three-dimensional polysiloxane network formed by hydrolysis and polycondensation reaction using γ-aminopropyltrialkoxysilane as a raw material;

[0010] (b) A hyaluronic acid network formed by disulfide bond crosslinking of thiolized hyaluronic acid through dissolved oxygen oxidation under the catalysis of amino groups in a polysiloxane network;

[0011] The disulfide bond network and the polysiloxane network interpenetrate to form a three-dimensional cross-linked injectable dual-network hydrogel.

[0012] Secondly, the present invention provides a method for preparing the above-mentioned dual-network hydrogel, specifically including the following steps:

[0013] (a) Preparation of polysiloxane solution;

[0014] (b) Preparation of a thiolized hyaluronic acid solution;

[0015] (c) The solutions described in steps (a) and (b) are mixed in a specific ratio. The mixed solution loses its fluidity within a short time, thus obtaining the dual-network hydrogel. This method is simple to operate, requires no exogenous oxidant, and can complete the preparation of the hydrogel at room temperature.

[0016] The preparation method of the polysiloxane solution includes the following steps:

[0017] γ-aminopropyltrialkoxysilane was dissolved in deionized water and stirred at room temperature for 80-300 min. The alcohols produced during the hydrolysis process were removed by rotary evaporation at 50 °C. The solution was then diluted to the original volume using a volumetric flask to obtain a polysiloxane solution.

[0018] Preferably, the γ-aminopropyltrialkoxysilane can be at least one of 3-aminopropyltrimethoxysilane and 3-aminopropyltriethoxysilane.

[0019] Preferably, the concentration of the polysiloxane is 1%-5%, more preferably 2%-4%.

[0020] The method for preparing the thiolized hyaluronic acid solution includes the following steps:

[0021] Sodium hyaluronate powder was dissolved in deionized water. 1-hydroxybenzotriazole (HOBT) and 1-(3-dimethylaminopropyl)-3-ethylcarbodiimide hydrochloride (EDCI) were added under ice bath conditions. After activation at room temperature for 2 h, L-cysteine ​​methyl ester hydrochloride (L-Cys-OMe·HCl) was added to the reaction system. The reaction was then carried out at room temperature under an argon atmosphere for 24 h. Subsequently, the solution was transferred to a dialysis bag and dialyzed with deionized water at pH 3.0 at room temperature for 3 days. The solution was then freeze-dried to obtain thiolated hyaluronic acid, which was dissolved in a suitable solution to obtain a thiolated hyaluronic acid solution.

[0022] Preferably, the molecular weight of hyaluronic acid is 1 kDa-400 kDa; more preferably, it is 200 kDa-400 kDa.

[0023] Preferably, the concentration of thiolated hyaluronic acid is 1%-5%; more preferably, it is 2%-4%.

[0024] Preferably, the thiol content of the thiolized hyaluronic acid is 20 μmol / g-180 μmol / g; more preferably, it is 60 μmol / g-100 μmol / g.

[0025] Preferably, the solution for dissolving hyaluronic acid can be at least one of pure water, PBS, or 0.9% sodium chloride, with PBS or 0.9% sodium chloride being the most preferred.

[0026] Thirdly, the dual-network hydrogel provided by this invention has good biocompatibility, wet tissue adhesion, injectability and suitable in vivo degradation rate, and can be used to prepare medical barrier materials for preventing postoperative tissue adhesion.

[0027] In practical use, the hydrogel can be formed by mixing a polysiloxane solution and a mercapto-modified hyaluronic acid solution, and applied to surgical wounds or damaged tissue surfaces via injection. Due to the dynamic disulfide cross-linking structure within the hydrogel, it exhibits shear-thinning properties under shear stress, allowing for smooth application via syringe and rapid restoration to a stable gel state after injection. This makes it suitable for minimally invasive surgery and covering irregular wounds.

[0028] Furthermore, the thiol groups in the hydrogel can interact with thiol groups on the tissue surface, enabling the hydrogel to form reliable adhesion on wet tissue surfaces, thereby reducing the risk of material migration. Simultaneously, due to the introduction of the polysiloxane network, the resulting dual-network hydrogel exhibits a slower degradation rate in vivo, continuously acting as a physical barrier during the critical time window for adhesion formation. After completing its anti-adhesion function, it gradually degrades and is eliminated through metabolism, demonstrating good biocompatibility.

[0029] The present invention has the following advantages over the prior art:

[0030] Compared with the prior art, the dual-network hydrogel provided by the present invention has the following significant advantages:

[0031] (1) Good wet tissue adhesion properties: It is beneficial for the material to exist stably in the target area without the need for additional fixation;

[0032] (2) Improved long-term stability: The polysiloxane network improves the stability of the hydrogel structure and the retention time in vivo, providing a reliable barrier effect throughout the adhesion formation cycle;

[0033] (3) Strong injectability and adaptability: It can cover irregular wounds and is better suited for minimally invasive scenarios;

[0034] (4) It can catalyze the rapid oxidation and cross-linking of disulfide bonds without the need for additional oxidants, reducing potential irritation and the risk of small molecule residues;

[0035] (5) Simple preparation: It can be quickly gelled after mixing at room temperature, which is convenient for clinical application.

[0036] (6) It has good biocompatibility and can meet the requirements for the use of anti-adhesion materials. Attached Figure Description

[0037] Figure 1 This is a SEM image of an injectable polysiloxane / hyaluronic acid dual-network hydrogel prepared in Example 1 of the present invention.

[0038] Figure 2 This is a photograph of the hydrogel prepared in Example 1;

[0039] Figure 3 The rheological test results are for the materials prepared in Example 1 and Comparative Examples 1-2;

[0040] Figure 4 The results of hemolytic performance tests are for the materials prepared in Example 1 and Comparative Example 2.

[0041] Figure 5 The results of the cell compatibility test are for the hydrogel prepared in Example 1;

[0042] Figure 6 The results are the injectability test results of the hydrogel prepared in Example 1;

[0043] Figure 7 The results are the in vivo degradation rate test results of the hydrogel prepared in Example 1;

[0044] Figure 8 The results are the test results of the anti-tissue adhesion performance of the hydrogel prepared in Example 1. Detailed Implementation

[0045] To further illustrate the present invention, the following describes in detail, with reference to embodiments, the injectable polysiloxane / hyaluronic acid dual-network hydrogel provided by the present invention, its preparation method, and its postoperative anti-adhesion application.

[0046] The following are some preferred embodiments of the present invention to further explain the advantages of the present invention. However, the following description is only for explaining the present invention and does not limit its content.

[0047] Example 1

[0048] Example 1 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel, specifically including the following steps:

[0049] (1) Preparation of polysiloxane solution: Add 4.8 g of 3-aminopropyltriethoxysilane to 5 mL of ultrapure water, stir the reaction at room temperature for 80 min, remove the ethanol produced by hydrolysis by rotary evaporation under reduced pressure at 40 °C for 90 min, and then make up to 10 mL with a volumetric flask to obtain a 48 wt% polysiloxane solution.

[0050] (2) Preparation of thiolized hyaluronic acid solution: 1.6 g of hyaluronic acid with a molecular weight of 400 kDa was added to 320 mL of deionized water and stirred vigorously until completely dissolved. Then, 460.4 mg of HOBT and 6134.4 mg of EDCI were added to the solution under ice bath conditions and mixed well. The mixture was activated at room temperature for 2 h. Then, 1373.2 mg of L-Cys-OMe·HCl was added to the reaction system. After purging with argon gas for 20 min, the reaction was maintained under an argon atmosphere and stirred at room temperature for 24 h. After the reaction was completed, the reaction mixture was dialyzed at room temperature for 3 days using a dialysis bag with a molecular weight cutoff of 8 kDa-14 kDa. The water was changed every 6 h. The dialysate was deionized water containing 5 mmol / L HCl and 2 μmol / L EDTA. The reaction solution was then freeze-dried to obtain thiolized hyaluronic acid. The thiolized hyaluronic acid was then added to PBS at pH=7.4 and vortexed to obtain a 2% thiolized hyaluronic acid solution.

[0051] (3) The above polysiloxane solution and mercapto-modified hyaluronic acid solution are mixed at a volume ratio of 2:25. After vortexing and mixing, the mixture can be rapidly crosslinked and lose its fluidity at room temperature to obtain a polysiloxane / hyaluronic acid dual-network hydrogel.

[0052] The SEM images and physical images of the polysiloxane / hyaluronic acid dual-network hydrogel prepared in this embodiment are shown below. Figure 1 and Figure 2 As shown, for easy distinction, the material in Example 1 is named HAS / APTESH.

[0053] Example 2

[0054] Example 2 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel. The difference between Example 1 and Example 2 is that the γ-aminopropyltrialkoxysilane used to prepare the polysiloxane solution is different. Example 2 uses 3-aminopropyltrimethoxysilane. The other steps are roughly the same as in Example 1 and will not be repeated here.

[0055] Example 3

[0056] Example 3 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel. The difference from Example 1 is that the molecular weight of the raw materials used to prepare the thiolized hyaluronic acid solution is different.

[0057] Example 3 describes the preparation of a thiolized hyaluronic acid solution as follows: 1.6 g of hyaluronic acid with a molecular weight of 1 kDa was added to 320 mL of deionized water and stirred vigorously until completely dissolved. Then, 460.4 mg of HOBT and 6134.4 mg of EDCI were added under ice bath conditions and mixed thoroughly. The mixture was activated at room temperature for 2 h. Then, 1373.2 mg of L-Cys-OMe·HCl was added to the reaction system. After purging with argon gas for 20 min, the reaction was maintained under an argon atmosphere and stirred at room temperature for 24 h. After the reaction was complete, the reaction mixture was dialyzed for 3 days at room temperature using a dialysis bag with a molecular weight cutoff of 200-400 Da, with the water changed every 6 h. The dialysate was deionized water containing 5 mmol / L HCl and 2 μmol / L EDTA. The reaction solution was then freeze-dried to obtain thiolized hyaluronic acid. The thiolized hyaluronic acid was then added to PBS at pH 7.4 and vortexed to obtain a 2% thiolized hyaluronic acid solution. The other steps are largely the same as in Example 1, and will not be repeated here.

[0058] Example 4

[0059] Example 4 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel. The difference from Example 1 lies in the amount of L-Cys-OMe·HCl added to prepare the thiolized hyaluronic acid solution. In Example 4, 2746.4 mg of L-Cys-OMe·HCl was added; the other steps are largely the same as in Example 1 and will not be repeated here.

[0060] Example 5

[0061] Example 5 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel. The difference from Example 1 is that the solution for dissolving the thiolized hyaluronic acid is different. In Example 5, the solution for dissolving the thiolized hyaluronic acid is 0.9% sodium chloride. The other steps are roughly the same as in Example 1, and will not be described again here.

[0062] Example 6

[0063] Example 6 provides a method for preparing an injectable polysiloxane / hyaluronic acid dual-network hydrogel. The difference from Example 1 is that the volume ratio of the polysiloxane solution and the thiolized hyaluronic acid solution is different. In Example 6, the volume ratio of the polysiloxane solution and the thiolized hyaluronic acid solution is 1:25. The other steps are roughly the same as in Example 1, and will not be repeated here.

[0064] Comparative Example 1

[0065] The preparation steps of the polysiloxane solution in Comparative Example 1 were the same as those in Example 1, except that in Comparative Example 1, unmodified hyaluronic acid solution was used instead of thiolized hyaluronic acid solution for step (3) to verify the effect of hyaluronic acid thiolization on the hydrogel. For ease of distinction, the material prepared in Comparative Example 1 was named HA / APTESH.

[0066] Comparative Example 2

[0067] The preparation steps of the thiolized hyaluronic acid solution in Comparative Example 2 were the same as those in Example 1, except that PBS was used instead of the polysiloxane solution in step (3) of Comparative Example 2 to verify the effect of the polysiloxane network on the hydrogel. For ease of distinction, the material prepared in Comparative Example 2 was named HAS.

[0068] The relevant tests are as follows:

[0069] 1. The rheological properties of the materials prepared in Example 1 and Comparative Examples 1-2 were measured. The results are as follows: Figure 3 As shown, the polysiloxane / hyaluronic acid dual-network hydrogel exhibits significant gel-forming characteristics, with a storage modulus (G') much higher than the loss modulus (G"), while this phenomenon was not observed in the materials of Comparative Example 1 and Comparative Example 2. This indicates that the thiolization modification of hyaluronic acid and the polysiloxane network play crucial roles in this hydrogel system, and neither can be omitted.

[0070] 2. The hemolytic properties of the materials prepared in Example 1 and Comparative Example 2 were tested to verify the blood compatibility of the hydrogel prepared in Example 1.

[0071] 1 mL of the hydrogel prepared in Example 1 was soaked in 2 mL of PBS at 37 °C for 24 h. The supernatant was collected by centrifugation to obtain the hydrogel extract, which is referred to as Gel for easy distinction.

[0072] 1 mL of the material prepared in Comparative Example 2 was soaked in 2 mL of PBS at 37 °C for 24 h. After centrifugation, the supernatant was collected to obtain the thiolized hyaluronic acid extract, which was referred to as HAS for easy distinction.

[0073] Then, 200 μL of 2% sheep erythrocyte suspension was mixed with 200 μL of hydrogel extraction buffer or 200 μL of thiolated hyaluronic acid extraction buffer, and incubated at 37 ℃ for 1 h. Afterward, it was centrifuged at 800 rpm for 10 min, and the hemolysis was observed by photographing. The absorbance of the supernatant was measured at 545 nm. PBS was used as the negative control group, and distilled water was used as the positive control group. The results are as follows: Figure 4As shown, neither the hydrogel extract nor the thiolized hyaluronic acid extract caused significant hemolysis, indicating that the materials in Example 1 and Comparative Example 2 have good blood compatibility.

[0074] 3. Perform cell compatibility testing on the injectable polysiloxane / hyaluronic acid dual-network hydrogel prepared in Example 1.

[0075] The HEK-293T cell line was used for evaluation using the MTT assay. First, 1 mL of hydrogel was immersed in 5 mL of DMEM medium at 37 °C for 48 h. Then, this portion of the medium was sterilized by filtration through a 0.22 μm sterile filter to obtain the hydrogel extract. The hydrogel extract was then diluted with DMEM medium to obtain 20%, 40%, 60%, 80%, and 100% hydrogel extracts.

[0076] HEK-293T cells were seeded in 96-well plates and cultured for 24 h. The culture medium was then replaced with different concentrations of hydrogel extract and cultured for another 24 h. The culture medium was then discarded and fresh medium was added. MTT reagent was added, and the cells were incubated at 37°C for 4 h. Cell viability was then quantified by measuring the absorbance at 570 nm. Results are as follows: Figure 5 As shown, incubation with hydrogel extracts of different concentrations did not significantly affect the growth of HEK-293T cells, indicating that the hydrogel prepared in Example 1 has good cell compatibility.

[0077] 4. The injectable performance of the injectable polysiloxane / hyaluronic acid dual-network hydrogel prepared in Example 1 was tested.

[0078] The injectability of the hydrogel was evaluated using an injection force test. The hydrogel was placed in a 1 mL syringe and injected through 23 g, 27 g, and 30 g needles. The injection force was tested using a computer-controlled universal testing machine at a speed of 20 mm / min in compression mode. The maximum force during the entire test was defined as the injection force. Figure 6 As shown, the injection force required for the hydrogel prepared in Example 1 to be injected from the three types of needles all meet the standard that the maximum injection force of biomedical injectable materials should not exceed 80 N, indicating that the hydrogel is injectable.

[0079] 5. The in vivo degradation performance of the injectable polysiloxane / hyaluronic acid dual-network hydrogel prepared in Example 1 was determined.

[0080] The degradation rate of hydrogels was evaluated by subcutaneous implantation in the upper back of C57BL / 6J mice. Thirty mice were randomly divided into six groups of five mice each after a 7-day acclimatization period. 200 μL of sterile hydrogel was implanted into the upper back of each mouse using a 25 g needle. Mice were euthanized at specific time points after hydrogel injection, and the subcutaneous hydrogel was collected, photographed, and weighed. The remaining mass percentage of the hydrogel was calculated. Results are shown below. Figure 7 As shown, the hydrogel degraded to 42% of its initial mass in 84 days, indicating that the hydrogel prepared in Example 1 has a relatively slow degradation rate, which can meet the requirements for long-term prevention of tissue adhesion.

[0081] 6. The anti-adhesion performance of the injectable polysiloxane / hyaluronic acid dual-network hydrogel prepared in Example 1 was tested.

[0082] Twenty mice were randomly divided into an experimental group and a control group (n=10) after 7 days of acclimatization. Mice were anesthetized with 1 wt% Servetin 50. A 2 cm incision was made along the midline of the abdominal wall, and the cecum was exposed using a sterile cotton swab. The cecum was wiped back and forth 30 times with dry sterile gauze, and pinpoint bleeding was observed. Then, a surgical curette was used to rub the abdominal wall corresponding to the cecum 8 times, creating an abdominal wall defect. The experimental group received 0.2 mL of hydrogel to cover the wound, while the model group received 0.2 mL of PBS. Antibiotics were applied to the abdominal wall suture site to prevent infection. Five mice from each group were euthanized on postoperative days 7 and 14 to observe the adhesion between the abdominal wall and the cecum. Results are as follows: Figure 8 As shown, significant adhesions occurred between the abdominal wall and cecum in the control group mice at 7 and 14 days post-surgery, while no adhesions were observed between the abdominal wall and cecum in mice using the hydrogel prepared in Example 1 at both 7 and 14 days. The injectable polysiloxane / hyaluronic acid dual-network hydrogel provided by this invention can effectively prevent postoperative tissue adhesions.

[0083] The above description of the embodiments is only for the purpose of helping to understand the method and core ideas of the present invention. It should be noted that those skilled in the art can make several improvements and modifications to the present invention without departing from the principles of the present invention, and these improvements and modifications also fall within the protection scope of the claims of the present invention.

Claims

1. An injectable dual-network hydrogel, characterized in that, The hydrogel comprises: (a) A three-dimensional polysiloxane network formed by hydrolysis and polycondensation reaction using γ-aminopropyltrialkoxysilane as a raw material; (b) A hyaluronic acid network formed by disulfide bond crosslinking of thiolized hyaluronic acid through dissolved oxygen oxidation under the catalysis of amino groups in a polysiloxane network; The disulfide-crosslinked hyaluronic acid network and the polysiloxane three-dimensional network interpenetrate to form a three-dimensional crosslinked injectable dual-network hydrogel.

2. A method for preparing the injectable dual-network hydrogel as described in claim 1, characterized in that, Includes the following steps: (a) Mix γ-aminopropyltrialkoxysilane with water to allow it to undergo a hydrolysis reaction, thereby obtaining a polysiloxane solution; (b) Prepare thiolized hyaluronic acid and dissolve it in a suitable solution to obtain a hyaluronic acid solution; (c) The polysiloxane solution and the hyaluronic acid solution are mixed so that the thiolized hyaluronic acid is oxidized by dissolved oxygen under the catalysis of the amino groups in the polysiloxane network to form disulfide bonds, and finally a double network hydrogel is obtained.

3. The method for preparing an injectable dual-network hydrogel as described in claim 2, characterized in that, The γ-aminopropyltrialkoxysilane is selected from at least one of 3-aminopropyltrimethoxysilane and 3-aminopropyltriethoxysilane, and the final concentration of the polysiloxane is 1%-5%.

4. The method for preparing an injectable dual-network hydrogel as described in claim 2, characterized in that, In the hyaluronic acid solution, the molecular weight of hyaluronic acid is 1 kDa-400 kDa, the thiol content of thiolized hyaluronic acid is 20 μmol / g-180 μmol / g, the final concentration of thiolized hyaluronic acid is 1%-5%, and the dissolving solution is selected from at least one of pure water, PBS, or 0.9% sodium chloride.

5. The use of the injectable dual-network hydrogel of claim 1 in the preparation of a medical barrier material for postoperative anti-adhesion.

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