An anti-inflammatory, easily replaceable, adhesive hydrogel wound patch and a method for its preparation

Abstract

The application discloses an anti-inflammatory easily-replaced adhesive hydrogel adhesive plaster and a preparation method thereof, relates to the field of biomedical materials, and is a green-prepared hydrogel adhesive plaster based on lipoic acid / hyaluronic acid-g-lipoic acid / cellulose nanocrystals, which has excellent adhesion, tensile property and reusability, and has the abilities of anti-inflammation and promoting wound repair, and can be easily removed through water washing, has the function of being removed on demand, and can be applied to the treatment and healing of first-aid trauma wounds.

Description

Technical Field

[0001] This invention relates to the field of biomedical materials, specifically to an anti-inflammatory, easily replaceable adhesive hydrogel wound dressing and its preparation method. Background Technology

[0002] Wound dressings serve as a physical barrier, effectively resisting the invasion of external microorganisms, replacing normal skin. Their properties are crucial, including providing a favorable healing microenvironment, closing the wound, achieving timely hemostasis, and accommodating wound movement. Traditional wound dressings, including gauze, cotton, and sponges, cannot effectively close the wound or stop bleeding in a timely manner, while surgical sutures and staples are not effectively used in pre-hospital settings. During patient movement, the wound site also moves frequently, and traditional hydrogel wound dressings, due to insufficient tissue adhesion and mechanical properties, cannot meet the demands of wound movement, often resulting in breakage or displacement and infection. Addressing these pressing challenges, the development of high-strength, highly adhesive, anti-inflammatory wound dressings is essential for pre-hospital emergency care.

[0003] Currently, many strategies have been explored to prepare hydrogels with high adhesion and strength. However, the preparation processes are often cumbersome. One unavoidable aspect is the post-processing involved in gel preparation, including the removal of initiators, small molecules, and monomers, which limits their application in biomedical engineering. Most importantly, to ensure rapid wound healing, dressings need frequent changes. How to easily remove highly adhesive hydrogels without causing secondary damage to the wound is a challenge that researchers need to solve. Therefore, the simple, green synthesis of high-performance, and easily replaceable hydrogel wound dressings is of great significance and practical application value. Summary of the Invention

[0004] In order to solve the problems of the prior art, the purpose of this invention is to overcome the shortcomings of the existing technology and provide an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing and its preparation method. The prepared hydrogel is an anti-inflammatory hydrogel with high adhesion, high strength and easy replacement, which can be used to promote wound healing.

[0005] One of the objectives of this invention is to provide an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing, the specific technical solution of which is as follows:

[0006] An anti-inflammatory and easily replaceable adhesive hydrogel wound dressing, comprising the following components: hyaluronic acid-g-lipoic acid, cellulose nanocrystals, lipoic acid, tris(hydroxymethyl)aminomethane, and 1-vinylimidazole.

[0007] The second objective of this invention is to provide a method for preparing an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing, the specific technical solution of which is as follows:

[0008] A method for preparing an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing, the preparation process comprising the following steps:

[0009] Hyaluronic acid-g-lipoic acid, cellulose nanocrystals, and lipoic acid were sequentially dissolved in an aqueous solution of tris(hydroxymethyl)aminomethane. After thorough dissolution and homogenization, a first heating reaction was carried out to obtain a precursor solution. Then, 1-vinylimidazole was added dropwise to the precursor solution and mixed thoroughly. A second heating reaction was carried out to prepare G... HC Hydrogel wound dressing.

[0010] Preferably, the preparation process of the hyaluronic acid-g-lipoic acid is as follows:

[0011] Hyaluronic acid was dissolved in formamide and stirred at 95°C until the hyaluronic acid was completely dissolved. The mixture was then cooled to room temperature to obtain a second solution. 4-Dimethylaminopyridine was added to the second solution as a catalyst to obtain a third solution.

[0012] The thioctoyl imidazole solution was added to the third solution, and the mixture was stirred at room temperature for 4 hours. Then, potassium dihydrogen phosphate solution was added to neutralize the mixture to obtain the fourth solution.

[0013] The fourth solution was purified by dialysis to remove the solvent and impurities produced in the reaction, and then freeze-dried to collect the sample to obtain hyaluronic acid-g-lipoic acid.

[0014] More preferably, the preparation process of the thioctoyl imidazole solution is as follows:

[0015] The first solution was prepared by dissolving lipoic acid in N,N-dimethylformamide at room temperature.

[0016] N,N'-carbonyldiimidazole was added to the first solution and stirred at room temperature to fully activate the carboxyl group of the lipoic acid, thereby obtaining a lipoyl imidazole solution.

[0017] Preferably, the mass ratio of the hyaluronic acid-g-lipoic acid, the cellulose nanocrystals, and the lipoic acid is 2:(3-7):40.

[0018] Preferably, the hyaluronic acid-g-lipoic acid, the cellulose nanocrystals, and the lipoic acid are sequentially dissolved in an aqueous solution formed by tris(hydroxymethyl)aminomethane, and the dissolution is carried out thoroughly using a shaker.

[0019] Preferably, the parameters for the first heating reaction are: 30 min at 70°C.

[0020] Preferably, the parameters for the second heating reaction are: reaction at 70°C for 6 hours.

[0021] The third objective of this invention is to provide an application of an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing, the specific technical solution of which is as follows:

[0022] An anti-inflammatory, easily replaceable adhesive hydrogel wound dressing for the treatment and healing of skin wounds.

[0023] Preferably, the anti-inflammatory and easily replaceable adhesive hydrogel wound dressing can be detached from the skin by rinsing with water.

[0024] The fourth objective of this invention is to provide a hydrogel suitable for use in wound dressings, the structural formula of which is as follows:

[0025]

[0026] Among them, the "gray rhombus" part represents cellulose nanocrystals, the "..." part represents hydrogen bonds, and the "circular" part represents 1-vinylimidazole.

[0027] Compared with the prior art, the beneficial effects of the present invention are:

[0028] This invention provides a method for preparing an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing. HALA, CNC, LA, and 1-vinylimidazole are sequentially and fully dissolved in a Tris Base solution, and reacted at 70°C for 6 hours to form a high-strength, highly adhesive, anti-inflammatory hydrogel wound dressing. When applied to wound repair, the prepared hydrogel wound dressing exhibits strong adhesion, tensile elasticity, reusability, anti-inflammatory properties, and biocompatibility. It can effectively inhibit wound inflammation and promote wound repair, and can be easily removed by rinsing with water, providing an on-demand removal function. Attached Figure Description

[0029] Figure 1 These are test graphs showing the adhesive properties of the hydrogels prepared in the embodiments and comparative examples of this invention. Figure 1 (A) is a graph showing the adhesion properties of the hydrogel in Example 2 to the soft tissue of chicken. Figure 1 (B) is a graph showing the adhesion properties of the hydrogel in Example 2 to the surface of pigskin. Figure 1 (C) is a graph showing the overlap shear stress-tensile displacement of the hydrogels prepared in the examples and comparative examples. Figure 1 (D) represents the shear modulus of the hydrogels prepared in the examples and comparative examples;

[0030] Figure 2 This is a cyclic strain diagram of the hydrogel in Example 2 of this invention;

[0031] Figure 3 This is a burst pressure diagram of the hydrogels prepared in the embodiments and comparative examples of the present invention;

[0032] Figure 4 The mechanical properties of the hydrogels prepared in the embodiments and comparative examples of this invention;

[0033] Figure 5 The figures show the compressive stress-strain curves of the hydrogels prepared in the embodiments and comparative examples of this invention.

[0034] Figure 6 The compression modulus of the hydrogels prepared in the embodiments and comparative examples of this invention;

[0035] Figure 7 The diagram shows the compression modulus of the hydrogels prepared in the embodiments and comparative examples of this invention.

[0036] Figure 8 This is a graph showing the repeated adhesion performance test of the hydrogel in Example 2 of this invention, wherein... Figure 8 (A) is a photograph of the experiment. Figure 8 (B) is a graph showing the adhesive strength test data after repeated adhesion of the hydrogel;

[0037] Figure 9 These are macroscopic photographs showing the effects of hydrogel application in Example 2 of this invention and the natural recovery effect in the control group;

[0038] Figure 10 These are histological evaluation photographs of the hydrogel's effect in Example 2 of this invention and the natural recovery effect in the control group, wherein... Figure 10 (A) and (C) correspond to the seventh and fourteenth days of recovery in the blank group, respectively. Figure 10 (B) and Figure 10 (D) Corresponding to the use of G respectively HC2 Days 7 and 14 of hydrogel recovery. Detailed Implementation

[0039] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0040] To facilitate understanding, the English terms mentioned below will be explained first:

[0041] LA: Alpha-lipoic acid;

[0042] Tris Base: Tris(hydroxymethyl)aminomethane;

[0043] CNC: Cellulose nanocrystals;

[0044] DMF: N,N-dimethylformamide;

[0045] CDI: N,N'-carbonyldiimidazole;

[0046] LA-Im: Thioctyl imidazole;

[0047] HA: Hyaluronic acid;

[0048] DMAP: 4-Dimethylaminopyridine.

[0049] HALA: Hyaluronic acid-g-lipoic acid

[0050] A method for preparing an anti-inflammatory and easily replaceable adhesive hydrogel wound dressing is described in detail below:

[0051] Example 1:

[0052] 0.62 g of LA was dissolved in 3 mL of DMF at room temperature to prepare the first solution. 0.97 g of CDI was added to the first solution and stirred at room temperature for 1 h to fully activate the carboxyl group of lipoic acid, thus obtaining the LA-Im solution.

[0053] 1.9 g of HA was dissolved in 38 mL of formamide and stirred at 95 °C for 1 h. After the HA was completely dissolved, the mixture was cooled to room temperature to obtain a second solution. 0.62 g of DMAP was added to the second solution as a catalyst to obtain a third solution.

[0054] The LA-Im solution was added to the third solution, and the mixture was stirred at room temperature for 4 hours. Then, potassium dihydrogen phosphate solution was added to neutralize the mixture until it reached neutral, thus obtaining the fourth solution.

[0055] The fourth solution was purified by dialysis to remove the solvent and impurities produced in the reaction, and then freeze-dried to collect the sample to obtain hyaluronic acid-g-lipoic acid, labeled as HALA;

[0056] 20 mg of HALA, 30 mg of CNC, and 400 mg of LA were sequentially dissolved in a Tris-Base aqueous solution with a mass concentration of 16.67% ± 0.01%. After thorough dissolution using a shaker, the solution was reacted at 70°C for 30 min to obtain a precursor solution. Then, 50 μL of 1-vinylimidazole was added dropwise to the precursor solution and mixed thoroughly. The mixture was then reacted at 70°C for 6 h to prepare G. HC Hydrogel wound dressing, marked as: G HC1 .

[0057] Example 2:

[0058] The steps are basically the same as in Example 1, except that the amount of CNC used is replaced by 50 mg instead of 30 mg in Example 1, and the resulting G... HCHydrogel wound dressing, marked as: G HC2 .

[0059] Example 3:

[0060] The steps are basically the same as in Example 1, except that the amount of CNC used is replaced with 70 mg instead of 30 mg in Example 1. The resulting hydrogel wound dressing is labeled as: G HC3 .

[0061] Comparative Example 1:

[0062] 50 mg of CNC and 400 mg of LA were dissolved sequentially in 200 mL of Tris Base solution. After thorough dissolution using a shaker, the solution was heated at 70 °C for 30 min. Then, 50 μL of 1-vinylimidazole was added dropwise and mixed thoroughly. The solution was then reacted at 70 °C for 6 h to prepare G. HC Hydrogel wound dressing, marked as: G C .

[0063] Comparative Example 2:

[0064] The steps are basically the same as in Example 1, except that the amount of CNC used is replaced with 0 instead of 30 mg in Example 1. The resulting hydrogel wound dressing is labeled as: G H .

[0065] The structural formulas of the hydrogels prepared in Examples 1 to 3 above are expressed as follows:

[0066]

[0067] It should be noted that in this structural formula, the crosslinking agent HALA is introduced to crosslink with polythioctic acid through disulfide bonds and hydrogen bonds, giving it the ability to be molded. At the same time, CNC is introduced to form multiple binding sites with LA to generate strong hydrogen bond interactions.

[0068] The following describes the property tests of the various hydrogel wound dressings prepared in the above embodiments and comparative examples:

[0069] I. Adhesion Strength Test

[0070] To demonstrate that the prepared hydrogel is suitable for use on biological surfaces and exhibits stable adhesive properties, several sets of macroscopic experiments were conducted, such as... Figure 1 As shown, G HC2 Hydrogels can adhere to the soft tissues of chickens. Figure 1 (A) consists of the liver, kidney, heart, intestines, and pig skin, respectively, and, as shown in Figure 1. Figure 1 As shown in (B), when G HC2When the hydrogel adheres to the surface of pigskin, the pigskin is twisted significantly. HC2 The hydrogel remained firmly adhered to the pigskin surface, indicating that it has excellent adhesive properties. When used in wound dressings, it can be directly applied to the wound surface and remains stable during dynamic processes. Unlike traditional hydrogel dressings, it does not require gauze or other external fixation methods to cover the wound site to secure the dressing, thus avoiding wound infection.

[0071] Overlap shear tests were performed on Examples 1 to 3, as well as Comparative Examples 1 and 2, using a universal testing machine, and the shear modulus was further calculated. Figure 1 (C) and Figure 1 As shown in (D), G C G H G HC1 G HC2 and G HC3 The adhesive strengths of the five hydrogel wound dressing samples reached 26.94 kPa, 29.51 kPa, 24.41 kPa, 28.57 kPa and 20.7 kPa, respectively, and the shear moduli were 112.65±5.26 kPa, 105.23±7.67 kPa, 106.58±4.33 kPa, 114.39±9.38 kPa and 107.03±7.61 kPa, respectively, indicating that the prepared hydrogels all have excellent adhesive properties.

[0072] II. Self-healing performance test

[0073] 2.1 Alternating Strain Test

[0074] For G HC2 The hydrogel was subjected to low (1%) to high (500%) cyclic shear strain treatment, such as... Figure 2 As shown, under low strain conditions, the storage modulus of the system is greater than the loss modulus, exhibiting good elasticity. However, as the strain increases to 500%, the gel system ruptures, the loss modulus exceeds the storage modulus, and the system exhibits significant viscous behavior. Upon returning to the initial strain value, the system rapidly recovers to its original state, and the storage modulus does not show a significant decrease. This indicates that the adhesive hydrogel prepared based on thioctic acid possesses excellent self-healing properties.

[0075] 2.2 Burst Pressure Test

[0076] To investigate the hydrogel's ability to withstand blood pressure shocks and evaluate its rapid adhesion and sealing performance at the skin, simulated test conditions for hydrogels at skin wound sites. A layer with a concentration of 0.05 g / cm³ was uniformly applied around the notch of a rubber tube. 3After the gelatin was allowed to air dry naturally, the prepared hydrogel was tightly adhered to the notch and placed horizontally for 5 minutes. Then, the syringe was slowly pushed in to conduct a burst pressure test. The hydrogel inflated like a balloon, demonstrating its excellent energy dissipation properties. The peak pressure that the hydrogel withstood before pressure loss was taken as the burst pressure. Figure 3 As shown, G C G H G HC1 G HC2 and G HC3 The maximum burst pressures subjected to the five hydrogel samples in the first test were 27.67±1.53 kPa, 21.67±2.08 kPa, 36±2 kPa, 35.83±1.26 kPa, and 47±1 kPa, respectively. These results indicate that the prepared hydrogel samples all possess excellent adhesion strength. Due to the excellent adhesion and self-healing properties of the hydrogels, a second burst pressure test was conducted on the five hydrogel samples. After the first hydrogel failure, the testing device was placed horizontally for 10 minutes to allow the hydrogel to reorganize its cross-linked network through dynamic bonds, followed by the second burst test. The test results show that, compared to the results of the first burst, G... C G H G HC1 G HC2 and G HC3 The burst pressure values ​​of the five hydrogels decreased, being 23.33±1.53 kPa, 19.67±2.08 kPa, 29.67±1.53 kPa, 33.17±1.76 kPa, and 42.67±1.53 kPa, respectively. The results indicate that the hydrogels can still withstand a certain impact strength after self-healing and can serve as excellent sealing and hemostatic patches.

[0077] III. Mechanical Property Testing

[0078] 3.1 Relationship between frequency scanning and corresponding energy storage modulus and loss modulus

[0079] Using a rotational rheometer to measure G C G H G HC1 G HC2 and G HC3 Five hydrogel samples were tested for their mechanical properties. For example... Figure 4 As shown, under a strain of 1%, the storage modulus (G') of hydrogels in the oscillation frequency range from 0.1 Hz to 100 Hz was greater than the loss modulus (G”). The results indicate that the storage modulus was greater than the loss modulus, suggesting that all five hydrogel samples were elastic hydrogels. It was also found that G… HC1 G HC2 and G HC3The storage modulus of the three hydrogels compared to G C G H All showed significant improvement, and at 1 Hz, the storage modulus of the hydrogel increased with the increase of CNC addition.

[0080] 3.2 Compression Deformation Test

[0081] G was analyzed using a thermomechanical dynamics analyzer. C G H G HC1 G HC2 and G HC3 Five hydrogel samples were subjected to compression performance tests. Figure 5 As shown, under compressive stress of up to 450 kPa, the five samples exhibited G... C G H G HC1 G HC2 and G HC3 The deformation of the hydrogels were 82.37%, 83.93%, 78.82%, 81.19%, and 80.08%, respectively, and none of them broke, demonstrating extremely strong toughness. Figure 6 It is G C G H G HC1 G HC2 and G HC3 The compressive modulus was calculated using stress-strain ratios at strain percentages of 5% and 10%, and was 16.3±0.85 kPa, 11.43±0.82 kPa, 30.04±0.93 kPa, 29.96±0.81 kPa, and 29.24±0.57 kPa, respectively. HC1 G HC2 and G HC3 The compressive modulus of hydrogels compared to G C G H All increased significantly.

[0082] 3.3 Tensile property test

[0083] Using a universal testing machine to test G C G H G HC1 G HC2 and G HC3 Five hydrogel samples underwent cyclic tensile testing. For example... Figure 7 As shown, G C G H G HC1 G HC2 and G HC3The stress-strain curves of the hydrogel under cyclic tensile stress are shown. When the hydrogel is loaded to 200% strain and then the external force is immediately removed, a clear loop is observed in the cyclic tensile curves of all samples, but 50% deformation fatigue occurs. The hysteresis energies of the five hydrogels were calculated using the area under the loop of the curves as follows: 57.15±4.17 kPa, 48.57±3.79 kPa, 45.38±2.76 kPa, 49.83±2.05 kPa, and 67.06±2.73 kPa. This indicates that the hydrogel can effectively dissipate energy under large deformation, exhibiting excellent toughness.

[0084] IV. On-demand debonding test

[0085] G HC1 G HC2 and G HC3 Three hydrogel samples were adhered to the substrate. By rinsing the interface between the hydrogel and the substrate with water, the hydrogel and the substrate could be easily separated by hand.

[0086] V. Repeated Adhesion Performance Test

[0087] G HC2 The hydrogel adhered to a 100g weight. One end of the hydrogel was pinched and pulled upwards until the weight left the table. The gel was then rinsed with water to remove it, dried, and left for 10 minutes. It was then reattached to the 100g weight, and the test was repeated. Figure 8 As shown in (A), during the first adhesion, G HC3 Hydrogels can easily support a weight of 100g; during the second adhesion, G HC3 The hydrogel could still support a weight of 100g, but the adhesive strength decreased; on the third adhesion, it could barely support 100g, and slippage occurred at the adhesive interface; on the fourth re-adhesion, it could still easily support a weight of 50g. The adhesive strength of the hydrogel under repeated adhesion was tested using a universal testing machine. Figure 8 As shown in (B), the repeated adhesion performance of the hydrogel decreases with the increase of adhesion times, but it still maintains a large adhesion strength.

[0088] VI. pH Test

[0089] Using a pH meter to measure G C G H G HC1 G HC2 and G HC3The pH of the precursor solutions from the five hydrogel preparation processes, as well as the soaking solutions obtained after soaking in 10 mL of water for 5 minutes after preparation, was tested to analyze the safety of the hydrogels for use as wound dressings. As shown in Table 1, the precursor solutions were weakly alkaline, but the pH of the soaking solutions after gelation was close to neutral. This indicates that the prepared hydrogels will not have their application limited by acidity or alkalinity. The hydrogels were prepared under green and safe conditions and are within the biosafety range, making them suitable for use as wound dressings. Furthermore, LA is a small molecule drug commonly used clinically to treat diabetes, possessing anti-inflammatory and antioxidant functions. Therefore, LA, as a monomer, does not require post-processing such as dialysis after polymerization and exhibits excellent biocompatibility.

[0090] Table 1. pH values ​​of the soaking solutions and their respective precursor solutions for five different hydrogel samples.

[0091] sample Precursor solution Immersion solution of hydrogel <![CDATA[G C ]]> 8.5 7.4 <![CDATA[G H ]]> 8.2 7.2 <![CDATA[G HC1 ]]> 7.8 6.9 <![CDATA[G HC2 ]]> 7.8 6.9 <![CDATA[G HC3 ]]> 7.8 6.9

[0092] VII. Wound Repair in Rats

[0093] SD rats showed spontaneous wound healing of lacerations (blank group) and G HC2 The effects of using hydrogel, such as Figure 9 As shown, the effect of GHC2 hydrogel was significantly higher than that of the untreated control group. At fourteen days, G... HC2 The wound treated with hydrogel closed completely and was fully repaired, while the control group, which healed naturally, still had obvious incisions and scabs at the wound site, indicating that G... HC2 Hydrogels have a good effect on promoting wound healing.

[0094] Furthermore, to understand the effect on wound healing, the spontaneous recovery of laceration wounds in SD rats and the effect of G... HC2 Histological evaluation was performed on skin tissue samples recovered by hydrogel treatment. Skin tissue samples from the cuts collected on days 7 and 14 were stained with hematoxylin and eosin (H&E) and then observed under a microscope. Figure 10 As shown, on the seventh day, the control group still had some epidermal defects at the wound site, and the dermal tissue structure was loose. In contrast, the group using G... HC2 The sample's epidermis showed continuous adhesion and dense matrix deposition; while at fourteen days, G... HC2 The epidermis of the sample was dense, the dermal tissue was intact, and the wound showed obvious contraction. The growth of skin appendages could be clearly observed. In contrast, the control group still showed relatively obvious skin defects, indicating that G HC2 Hydrogel materials have a certain positive effect on promoting wound healing.

[0095] In summary, the hydrogel wound dressing prepared by the method provided in this invention has excellent tissue adhesion and high mechanical properties. It can be directly applied as a wound dressing, which can promptly adhere the skin on both sides of the wound together. At the same time, it can also act as a temporary barrier for the skin to prevent microbial invasion, thereby promoting wound healing.

[0096] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended embodiments and their equivalents.

Claims

1. A method of making an anti-inflammatory, easily replaceable, adhesive hydrogel wound covering, characterized in that, The hyaluronic acid-g-thioctic acid, cellulose nanocrystal and thioctic acid are sequentially dissolved in a tris(hydroxymethyl)aminomethane aqueous solution, and after being fully dissolved and uniformly mixed, a first heating reaction is performed to obtain a precursor solution; then 1-vinylimidazole is added dropwise into the precursor solution and uniformly mixed, and a second heating reaction is performed to prepare a G HC Water gel adhesive plaster The preparation process of the hyaluronic acid-g-thioctic acid is as follows: Dissolve the hyaluronic acid in formamide, and after stirring at 95 °C until the hyaluronic acid is completely dissolved, continue to cool to room temperature to obtain a second solution, add 4-dimethylaminopyridine as a catalyst to the second solution to obtain a third solution; Add the thioctyl imidazole solution to the third solution, stir at room temperature for 4 h, and then add a potassium dihydrogen phosphate solution to neutralize to neutral to obtain a fourth solution; Dialysis purification is performed on the fourth solution to remove solvents and impurities generated in the reaction, and then freeze-drying is performed to collect samples to obtain hyaluronic acid-g-thioctic acid.

2. A process for the preparation of an anti-inflammatory, easily replaceable, adhesive hydrogel plaster according to claim 1, characterized in that, The preparation process of the thioctyl imidazole solution is as follows: Dissolve thioctic acid in N,N-dimethylformamide at room temperature to prepare a first solution; Add N,N'-carbonyldiimidazole to the first solution, and stir at room temperature to fully activate the carboxyl group of the thioctic acid to obtain a thioctyl imidazole solution.

3. A process for the preparation of an anti-inflammatory, easily replaceable, adhesive hydrogel plaster according to claim 1, characterized in that, The mass ratio among the hyaluronic acid-g-thioctic acid, the cellulose nanocrystal, and the thioctic acid is 2: (3-7):

40.

4. A process for the preparation of an anti-inflammatory, easily replaceable, adhesive hydrogel plaster according to claim 1, characterized in that, The hyaluronic acid-g-thioctic acid, the cellulose nanocrystal, and the thioctic acid are sequentially dissolved in the aqueous solution of tris(hydroxymethyl)aminomethane, and an oscillator is used for sufficient dissolution.

5. The method of claim 1, wherein the anti-inflammatory, easily replaceable, adhesive hydrogel bandage is prepared by the steps of: The parameters of the first heating reaction are 70 °C heating for 30 min, and the parameters of the second heating reaction are 70 °C for 6 h.

6. An anti-inflammatory, easily replaceable, adhesive hydrogel wound covering, characterized in that, The adhesive plaster is prepared according to the method of any one of claims 1-5, and the component composition comprises hyaluronic acid-g-thioctic acid, cellulose nanocrystal, thioctic acid, tris(hydroxymethyl)aminomethane, and 1-vinylimidazole.

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