Preparation method of surgical anti-adhesion hydrogel material

Abstract

The invention belongs to the technical field of medical polymer materials, and particularly relates to a preparation method of a surgical anti-adhesion hydrogel material. The material is prepared from 2, 3-diformylbenzoic acid modified gelatin, 3, 4-dihydroxyphenylethylamine, sodium hyaluronate, sodium tripolyphosphate, hydrogen peroxide, ascorbic acid and a phosphate buffer solution. Modified gelatin powder is obtained through a grafting reaction of 2, 3-diformylbenzoic acid and gelatin, then the modified gelatin powder, 3, 4-dihydroxyphenylethylamine and an auxiliary agent are prepared into a main gel solution, hydrogen peroxide and ascorbic acid are added before use, and the main gel solution is quickly crosslinked into gel under the body temperature condition. The obtained hydrogel can be stably combined with the tissue surface, the degradation process is matched with tissue repair, and the hydrogel has a free radical scavenging effect. Animal experiments show that the material can effectively reduce abnormal adhesion between postoperative tissues and has a good clinical application prospect.

Description

Technical Field

[0001] This invention belongs to the field of medical polymer materials technology, specifically relating to a method for preparing a surgical anti-adhesion hydrogel material. Background Technology

[0002] After surgery, tissues and organs are often covered with blood and inflammatory exudates. These substances, under the influence of fibrin deposition and fibroblast proliferation, can easily lead to abnormal adhesions between adjacent tissues. Postoperative adhesions can cause complications such as chronic pain, intestinal obstruction, and infertility. They can also increase the difficulty of tissue separation and the risk of bleeding during secondary surgeries, adversely affecting patient recovery and clinical procedures.

[0003] Existing anti-adhesion materials mainly fall into three categories: polymeric barrier membranes, biodegradable films, and injectable hydrogels. Polymeric barrier membranes, such as hyaluronic acid membranes and polylactic acid membranes, typically function as isolation membranes on smooth wound surfaces, but they are difficult to adhere to in complex or irregular surgical areas, limiting their use in minimally invasive procedures. Biodegradable film materials have degradation rates that are difficult to match with the tissue healing process; excessively rapid degradation leads to loss of barrier function, while excessively slow degradation may hinder tissue repair. Injectable hydrogels can form gels in situ within body cavities, offering convenient manipulation, but common systems exhibit slow gelation rates, insufficient initial gel strength, limited adhesion to tissue surfaces, and a lack of adhesion-enhancing or anti-inflammatory / antioxidant functions.

[0004] Existing hydrogels mostly rely on single physical gelation or simple chemical cross-linking, making it difficult to simultaneously achieve the comprehensive properties of rapid gelation, stable adhesion, and controllable degradation. Some materials require long processing times or harsh reaction conditions for application, making it difficult to meet the requirements of high efficiency, protection, and safety in surgical procedures.

[0005] Existing anti-adhesion materials have limitations in terms of ease of operation, in-situ gelation ability, tissue adhesion, and degradation control. Developing a hydrogel material that can rapidly gel at body temperature, has good adhesion to tissue surfaces, and possesses suitable degradation properties has important application value. Summary of the Invention

[0006] To overcome the shortcomings of existing anti-adhesion materials in terms of ease of operation, in-situ gelation speed, tissue adhesion, and controllable degradation, the present invention aims to provide a method for preparing a surgical anti-adhesion hydrogel material. The technical solution adopted in this invention uses 2,3-dialdehyde benzoic acid-modified gelatin as the main skeleton material, introduces 3,4-dihydroxyphenylethylamine as a tissue adhesion enhancer, and supplements it with sodium hyaluronate and sodium tripolyphosphate as adjuvants. Simultaneously, it utilizes hydrogen peroxide and ascorbic acid to form a cross-linking system, prepares an injectable solution in phosphate buffer, and rapidly gels at body temperature to form a surgical anti-adhesion hydrogel. This material can rapidly gel at body temperature, possesses good tissue adhesion and suitable degradation properties, is easy to operate, and has a good postoperative anti-adhesion effect.

[0007] The objective of this invention can be achieved through the following technical solutions:

[0008] A surgical anti-adhesion hydrogel material comprises the following raw materials in parts by weight: 5-20 parts of 2,3-dialdehyde benzoic acid modified gelatin, 1-8 parts of 3,4-dihydroxyphenylethylamine, 0.5-3 parts of sodium hyaluronate, 0-3 parts of sodium tripolyphosphate, 0.1-1 parts of hydrogen peroxide, 0.1-1 parts of ascorbic acid, and 50-100 parts of phosphate buffer.

[0009] Optionally, the 2,3-dialdehyde benzoic acid modified gelatin comprises the following raw materials in parts by weight: 10-30 parts gelatin, 1-10 parts 2,3-dialdehyde benzoic acid, 1-5 parts N-hydroxysuccinimide, 1-5 parts 1-(3-dimethylaminopropyl)-3-ethylcarbodiimide hydrochloride, and 100-300 parts deionized water.

[0010] Optionally, the preparation method of 2,3-dialdehyde benzoic acid modified gelatin includes the following steps:

[0011] (1) Add gelatin to deionized water, heat and stir to dissolve it completely to obtain a gelatin solution;

[0012] (2) Mix 2,3-dialdehyde benzoic acid with N-hydroxysuccinimide and 1-(3-dimethylaminopropyl)-3-ethylcarbodiimide hydrochloride and activate to form an active ester;

[0013] (3) The activated 2,3-dialdehyde benzoic acid solution was slowly added dropwise to the gelatin solution, and the grafting reaction was carried out while stirring to obtain the modified gelatin solution;

[0014] (4) The obtained modified gelatin solution is placed into a dialysis bag and dialyzed to remove unreacted small molecule impurities;

[0015] (5) The dialysis solution was freeze-dried to obtain 2,3-dialdehyde benzoic acid modified gelatin powder.

[0016] Optionally, the reaction conditions for step (1) are a temperature of 40-50℃ and a stirring time of 30-60 minutes; the reaction conditions for step (2) are a reaction temperature of 20-30℃ and a reaction time of 15-30 minutes; the reaction conditions for step (3) are a dropping time of 10-30 minutes, a reaction pH of 6.5-7.5, a reaction temperature of 25-40℃, and a reaction time of 4-8 hours; the reaction conditions for step (4) are a dialysis bag molecular weight cutoff of 3500 Da, a dialysis time of 36-72 hours, and a water change frequency of once every 4-6 hours; the reaction conditions for step (5) are a freezing temperature of -20 to -80℃, a freeze-drying temperature of -50 to -60℃, and a freeze-drying time of 24-48 hours.

[0017] Optionally, the purity of 3,4-dihydroxyphenylethylamine is 95% to 99.9%.

[0018] Optionally, a method for preparing a surgical anti-adhesion hydrogel material includes the following steps:

[0019] S1, 2,3-dialdehyde benzoic acid modified gelatin, 3,4-dihydroxyphenylethylamine, sodium hyaluronate and sodium tripolyphosphate were added to phosphate buffer and stirred evenly to obtain the main gel solution;

[0020] S2, add hydrogen peroxide and ascorbic acid to the main gel solution, mix well and inject into the application site, forming a hydrogel at body temperature.

[0021] Optionally, the conditions for step S1 are: stirring temperature of 25-40°C and stirring time of 10-30 minutes; the conditions for step S2 are: hydrogen peroxide and ascorbic acid added in a 1:1 ratio, mixing time of 30-120 seconds, gelation temperature of 30-37°C, and gelation time of 2-5 minutes.

[0022] The beneficial effects of this invention are:

[0023] This invention introduces 2,3-dialdehyde benzoic acid groups into the gelatin molecular chain to form a stable dynamic Schiff base structure, enabling the modified gelatin to possess self-crosslinking and reversible repair capabilities, achieving controllable degradation while maintaining gel strength. This modification method differs from common physical gelation or simple chemical crosslinking, endowing the material with unique structural response characteristics.

[0024] This invention further introduces 3,4-dihydroxyphenylethylamine, whose phenolic hydroxyl and amino groups can form hydrogen bonds, π-π stacking, and phenolic quinone oxidative crosslinking with the aldehyde and carboxyl groups in the modified gelatin, thereby generating multi-point binding on the tissue surface. Compared with the unmodified system, this molecule significantly enhances the interfacial adhesion between the hydrogel and the wound tissue, and endows the material with antioxidant properties, reducing the adverse effects of postoperative inflammatory reactions.

[0025] The synergistic effect of the two components gives the resulting hydrogel a dual function that is difficult to achieve with conventional systems: first, the gel forms a stable bond with the tissue surface; second, the interfacial bonding is accompanied by an antioxidant protective effect, thus exhibiting higher reliability and stability in the process of preventing adhesion. Attached Figure Description

[0026] The invention will now be further described with reference to the accompanying drawings.

[0027] Figure 1 A bar chart comparing the gelation time of samples with different ratios;

[0028] Figure 2 A bar chart comparing the tissue adhesion of samples with different ratios;

[0029] Figure 3 A bar chart comparing the residual rates of samples with different ratios;

[0030] Figure 4 A bar chart comparing the antioxidant effects of samples with different formulation ratios;

[0031] Figure 5 A bar chart comparing the anti-adhesion scores of samples with different ratios. Detailed Implementation

[0032] The present invention will be further described below with reference to specific embodiments. However, the present invention is not limited to the following embodiments. Equivalent adjustments made without departing from the spirit and essence of the present invention should also be considered to fall within the protection scope of the present invention.

[0033] Example 1

[0034] The purpose of this embodiment is to verify the gelation rate and tissue adhesion properties of the hydrogel obtained under low ratio conditions.

[0035] S1. Dissolve 10 parts of gelatin in 100 parts of deionized water and stir at 45°C. Separately, dissolve 1 part of 2,3-dialdehyde benzoic acid, 1 part of N-hydroxysuccinimide, and 1 part of 1,3-dimethylaminopropyl-3-ethylcarbodiimide hydrochloride in 10 parts of deionized water and react at 25°C for 20 minutes to obtain an activated solution. Slowly add the activated solution dropwise to the gelatin solution, adjust the pH to 7.0, and stir for 4 hours. Dialyze the resulting reaction solution through a dialysis bag with a molecular weight cutoff of 3500 Da for 48 hours, and freeze-dry to obtain modified gelatin powder.

[0036] S2, take 5 parts of modified gelatin and dissolve it in 50 parts of phosphate buffer, add 1 part of 3,4-dihydroxyphenylethylamine, 0.5 parts of sodium hyaluronate and 0.5 parts of sodium tripolyphosphate, stir evenly to obtain the main gel solution;

[0037] S3: Add 0.1 parts hydrogen peroxide and 0.1 parts ascorbic acid to the forward master gel solution, mix for 30 seconds, and inject into the model wound at 37°C. A stable hydrogel will form within 2 minutes.

[0038] Example 2

[0039] The purpose of this embodiment is to verify the balance between gelation rate and tissue adhesion of the hydrogel obtained under medium ratio conditions.

[0040] S1, dissolve 20 parts of gelatin in 200 parts of deionized water and stir at 45°C; separately, dissolve 5 parts of 2,3-dialdehyde benzoic acid, 3 parts of N-hydroxysuccinimide, and 3 parts of 1,3-dimethylaminopropyl-3-ethylcarbodiimide hydrochloride in 20 parts of deionized water and react at 25°C for 25 minutes to obtain an activated solution; slowly add the activated solution dropwise to the gelatin solution, adjust the pH to 7.2, and stir for 6 hours; after dialysis for 60 hours, freeze-dry the reaction solution to obtain modified gelatin powder;

[0041] S2, take 12 parts of modified gelatin and dissolve it in 80 parts of phosphate buffer, add 4 parts of 3,4-dihydroxyphenylethylamine, 2 parts of sodium hyaluronate and 1.5 parts of sodium tripolyphosphate, stir evenly to obtain the main gel solution;

[0042] S3: Add 0.5 parts hydrogen peroxide and 0.5 parts ascorbic acid to the forward master gel solution, mix for 60 seconds, and inject into the model wound at 37°C. Dense hydrogel will form within 3 minutes.

[0043] Example 3

[0044] The purpose of this embodiment is to verify the tissue adhesion and antioxidant capacity of the hydrogel obtained under high ratio conditions.

[0045] S1, dissolve 30 parts of gelatin in 300 parts of deionized water and stir at 50°C; separately, dissolve 10 parts of 2,3-dialdehyde benzoic acid, 5 parts of N-hydroxysuccinimide, and 5 parts of 1,3-dimethylaminopropyl-3-ethylcarbodiimide hydrochloride in 30 parts of deionized water and react at 28°C for 30 minutes to obtain an activated solution; add the activated solution dropwise to the gelatin solution, adjust the pH to 7.5, and stir for 8 hours; after dialysis for 72 hours, freeze-dry the reaction solution to obtain modified gelatin powder;

[0046] S2, take 20 parts of modified gelatin and dissolve it in 100 parts of phosphate buffer, add 8 parts of 3,4-dihydroxyphenylethylamine, 3 parts of sodium hyaluronate and 3 parts of sodium tripolyphosphate, stir evenly to obtain the main gel solution;

[0047] S3: Add 1 part hydrogen peroxide and 1 part ascorbic acid to the forward master gel solution, mix for 90 seconds, and inject into the model wound at 37°C. A high-strength hydrogel will form within 5 minutes.

[0048] Comparative Example 1

[0049] The purpose of this comparative example is to examine the gelling properties and tissue adhesion of the hydrogel obtained without the use of 2,3-dialdehyde benzoic acid-modified gelatin.

[0050] S1, 20 parts of gelatin were dissolved in 200 parts of deionized water and stirred at 45°C to dissolve; without adding 2,3-dialdehyde benzoic acid, N-hydroxysuccinimide and 1,3-dimethylaminopropyl-3-ethylcarbodiimide hydrochloride, a gelatin solution was obtained directly; after dialyzing under the same conditions for 60 hours, unmodified gelatin powder was obtained by freeze drying;

[0051] S2, take 12 parts of unmodified gelatin and dissolve it in 80 parts of phosphate buffer, add 4 parts of 3,4-dihydroxyphenylethylamine, 2 parts of sodium hyaluronate and 1.5 parts of sodium tripolyphosphate, stir evenly to obtain the main gel solution;

[0052] S3, using a forward master gel solution with 0.5 parts hydrogen peroxide and 0.5 parts ascorbic acid added, mixed for 60 seconds, and injected into the model wound at 37°C, showed a significant decrease in gelation rate and adhesion.

[0053] Comparative Example 2

[0054] The purpose of this comparative example is to examine the gelling properties and tissue adhesion of the hydrogel obtained without the introduction of 3,4-dihydroxyphenylethylamine.

[0055] S1, dissolve 20 parts of gelatin in 200 parts of deionized water and stir at 45°C; separately, dissolve 5 parts of 2,3-dialdehyde benzoic acid, 3 parts of N-hydroxysuccinimide, and 3 parts of 1,3-dimethylaminopropyl-3-ethylcarbodiimide hydrochloride in 20 parts of deionized water and react at 25°C for 25 minutes to obtain an activated solution; slowly add the activated solution dropwise to the gelatin solution, adjust the pH to 7.2, and stir for 6 hours; after dialysis for 60 hours, freeze-dry the reaction solution to obtain modified gelatin powder;

[0056] S2, take 12 parts of modified gelatin and dissolve it in 80 parts of phosphate buffer. Do not add 3,4-dihydroxyphenylethylamine, but only add 2 parts of sodium hyaluronate and 1.5 parts of sodium tripolyphosphate. Stir well to obtain the main gel solution.

[0057] S3, using a forward master gel solution with 0.5 parts hydrogen peroxide and 0.5 parts ascorbic acid added, mixed for 60 seconds, and injected into the model wound at 37°C, showed normal gelation rate but insufficient tissue adhesion.

[0058] Performance testing

[0059] 1. Gel formation time test

[0060] The purpose of this test was to verify the effect of different ratios and components on the gelation rate of hydrogels under body temperature conditions. 1 mL of the master gel solution from each example and comparative example was injected into the bottom of a transparent glass bottle and placed in a 37°C constant temperature water bath. A stopwatch was immediately started. The bottle was tilted 30 degrees every 10 seconds to observe whether the solution flowed. The time required for the solution to completely lose its fluidity was recorded as the gelation time. Each sample was repeated three times, and the average value was taken.

[0061] 2. Tissue adhesion test

[0062] The purpose of this test was to evaluate the adhesion ability of different hydrogel formulations to tissue surfaces. Fresh pig liver tissue was cut into 2 cm × 2 cm pieces, and the surfaces were washed with physiological saline and dried. The samples were injected into a gel at 37°C and applied to the tissue surface, then allowed to stand for 5 minutes. Subsequently, the tissue and gel were fixed separately to the fixtures of an electronic tensile testing instrument, and a 90-degree peel test was performed at a tensile speed of 10 mm per minute, recording the maximum peel force.

[0063] 3. In vitro degradation performance test

[0064] The purpose of this test was to compare the degradation behavior of different hydrogels in a bodily fluid environment. Prepared disc-shaped hydrogel samples were placed in phosphate buffer containing lysozyme and stored in a 37°C constant temperature shaking incubator. Samples were removed daily, surface moisture was removed, and the remaining mass was recorded. Degradation trends for each group of samples were plotted after 7 and 14 days.

[0065] 4. Antioxidant performance test

[0066] The purpose of this test was to investigate the antioxidant activity of the hydrogel after the introduction of 3,4-dihydroxyphenylethylamine. The sample solution was mixed with an ethanol solution and reacted in the dark for 30 minutes. The absorbance was then measured at 517 nm using a UV spectrophotometer and compared with a blank control group to evaluate the free radical scavenging effect.

[0067] 5. Evaluation of anti-adhesion effect

[0068] The purpose of this test was to verify the actual anti-adhesion effect of hydrogels in vivo using an animal model. A rat cecal abrasion model was established by gently rubbing the cecal surface to create a bleeding wound. Animals were randomly assigned to groups and injected with the hydrogels from the example and comparative examples, respectively. Fourteen days post-surgery, the animals were sacrificed, the abdominal cavity was opened, and the adhesion status was observed and scored. The scoring criteria included adhesion area, adhesion strength, and adhesion extent; lower scores indicated better anti-adhesion effects. Table 1 shows the performance test results.

[0069] sample Gel formation time (min) Tissue adhesion (N / cm²) 7-day residual rate (%) 14-day residual rate (%) Antioxidant effect (%) Anti-adhesion score Example 1 3.0 0.45 65 40 35 1.5 Example 2 2.0 0.60 75 55 60 0.5 Example 3 4.0 0.55 70 45 50 1.0 Comparative Example 1 6.0 0.20 40 20 10 3.0 Comparative Example 2 5.5 0.30 55 30 15 2.5

[0070] According to the data in the table, Figure 1 The gelation time results showed that Examples 1, 2, and 3 completed gelation within 3.0 minutes, 2.0 minutes, and 4.0 minutes, respectively, all significantly faster than Comparative Example 1 (6.0 minutes) and Comparative Example 2 (5.5 minutes). This indicates that the modified gelatin plays a crucial role in improving crosslinking efficiency, and the presence of 3,4-dihydroxyphenylethylamine further promotes rapid crosslinking, making the operation of these examples more suitable for the need for immediate gelation during surgery.

[0071] exist Figure 2 Regarding adhesion to the tissue interface, Example 2 achieved the highest value of 0.60 N / cm², followed by Example 3 at 0.55 N / cm², Example 1 at 0.45 N / cm², while Comparative Examples 1 and 2 were only 0.20 N / cm² and 0.30 N / cm², respectively. The data indicate that 3,4-dihydroxyphenylethylamine significantly improved the adhesion between the gel and the tissue interface, while 2,3-dialdehyde benzoic acid-modified gelatin provided more reaction sites; the synergistic effect of both significantly enhanced the adhesion performance.

[0072] Figure 3 The degradation performance showed that Example 2 had a 7-day residual rate of 75% and a 14-day residual rate of 55%, which was higher than that of Example 1 (65% and 40%) and Example 3 (70% and 45%), while Comparative Example 1 had only 40% and 20% and Comparative Example 2 had 55% and 30%. This indicates that Example 2 not only maintained a stable morphology in the early stage, but also degraded gradually in the later stage, providing an anti-adhesion barrier without affecting tissue repair due to prolonged residue.

[0073] Figure 4 It can be seen that in terms of antioxidant performance, the free radical scavenging effect of Example 2 reached 60%, Example 3 50%, and Example 1 35%, which is much higher than the 10% of Comparative Example 1 and the 15% of Comparative Example 2. This indicates that 3,4-dihydroxyphenylethylamine, as a functional small molecule, effectively plays an antioxidant role in the system, which can reduce the postoperative local inflammatory response and has added value in preventing adhesions.

[0074] Figure 5 In terms of anti-adhesion scoring, Example 2 scored only 0.5, the lowest level, indicating almost no obvious adhesion; Example 3 and Example 1 scored 1.0 and 1.5 respectively, showing good performance; Comparative Example 1 scored 3.0, indicating large-area adhesion that was difficult to separate; Comparative Example 2 scored 2.5, still showing a large area of ​​adhesion. The results show that the examples, especially Example 2, have the most outstanding anti-adhesion effect in vivo.

[0075] Based on the above data, Example 2 showed the best performance across all performance indicators, particularly demonstrating comprehensive advantages in terms of moderate gelation time, highest tissue adhesion, reasonable degradation process, strongest antioxidant capacity, and lowest anti-blocking score. Examples 1 and 3 were second best, also significantly superior to Comparative Examples 1 and 2. These results fully demonstrate that the synergistic design of 2,3-dialdehyde benzoic acid-modified gelatin and 3,4-dihydroxyphenylethylamine used in this invention effectively improves the overall performance of the hydrogel and exhibits significant innovative effects in anti-blocking applications.

Claims

1. A surgical anti-adhesion hydrogel material, characterized in that, The raw materials include 2,3-dialdehyde benzoic acid modified gelatin 5-20 parts, 3,4-dihydroxyphenethylamine 1-8 parts, sodium hyaluronate 0.5-3 parts, sodium tripolyphosphate 0-3 parts, hydrogen peroxide 0.1-1 part, ascorbic acid 0.1-1 part, and phosphate buffer 50-100 parts.

2. A surgical anti-adhesion hydrogel material according to claim 1, characterised in that, The 2,3-dialdehyde benzoic acid modified gelatin includes the following raw materials: gelatin 10-30 parts, 2,3-dialdehyde benzoic acid 1-10 parts, N-hydroxysuccinimide 1-5 parts, 1-(3-dimethylaminopropyl)-3-ethyl carbodiimide hydrochloride 1-5 parts, and deionized water 100-300 parts.

3. A surgical anti-adhesion hydrogel material according to either of claims 1 or 2, characterised in that, The preparation method of the 2,3-dialdehyde benzoic acid modified gelatin includes the following steps: (1) gelatin is added to deionized water, heated and stirred to fully dissolve, to obtain a gelatin solution; (2) 2,3-dialdehyde benzoic acid is mixed with N-hydroxysuccinimide and 1-(3-dimethylaminopropyl)-3-ethyl carbodiimide hydrochloride to form an active ester; (3) the activated 2,3-dialdehyde benzoic acid solution is slowly added to the gelatin solution, stirring is maintained to perform grafting reaction, to obtain a modified gelatin solution; (4) the obtained modified gelatin solution is loaded into a dialysis bag, dialysis is performed to remove unreacted small molecule impurities; (5) the dialyzed solution is freeze-dried to obtain 2,3-dialdehyde benzoic acid modified gelatin powder.

4. A surgical anti-adhesion hydrogel material according to claim 3, characterised in that, The reaction conditions of step (1) are temperature 40-50℃ and stirring time 30-60 minutes; the reaction conditions of step (2) are reaction temperature 20-30℃ and reaction time 15-30 minutes; the reaction conditions of step (3) are dropwise adding time 10-30 minutes, reaction pH value 6.5-7.5, reaction temperature 25-40℃, and reaction time 4-8 hours; the reaction conditions of step (4) are that the molecular weight cut-off of the dialysis bag is 3500 Da, dialysis time is 36-72 hours, and water changing frequency is once every 4-6 hours; and the reaction conditions of step (5) are freezing temperature -20--80℃, freeze-drying temperature -50--60℃, and freeze-drying time 24-48 hours.

5. A surgical anti-adhesion hydrogel material according to claim 1, wherein, The purity of the 3,4-dihydroxyphenethylamine is 95%-99.9%.

6. A method for the preparation of a surgical anti-adhesive hydrogel material as defined in any one of claims 1 to 5, characterized in that The method includes the following steps: S1, 2,3-dialdehyde benzoic acid modified gelatin, 3,4-dihydroxyphenethylamine, sodium hyaluronate, and sodium tripolyphosphate are added to phosphate buffer, stirred uniformly to obtain a main gel solution; S2, hydrogen peroxide and ascorbic acid are added to the main gel solution, mixed uniformly, and then injected at the use site to form a hydrogel under body temperature conditions.

7. A surgical anti-adhesion hydrogel material according to claim 6, wherein, The conditions of step S1 are stirring temperature 25-40℃ and stirring time 10-30 minutes; and the conditions of step S2 are that hydrogen peroxide and ascorbic acid are added in a 1:1 ratio, mixing time is 30-120 seconds, gel forming temperature is 30-37℃, and gel forming time is 2-5 minutes.

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