Multifunctional in-situ repair hydrogel based on modified dermal matrix as well as preparation method and application of multifunctional in-situ repair hydrogel
The multifunctional hydrogel formed by the dynamic covalent cross-linking of modified dermal matrix and borate ester solves the problems of single function, poor adhesion and insufficient mechanical properties of existing hydrogel dressings. It achieves seamless wound adhesion and self-healing, and has antibacterial, antioxidant and anti-inflammatory functions, making it suitable for the clinical treatment of chronic wounds.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- THE AFFILIATED SIR RUN RUN SHAW HOSPITAL OF SCHOOL OF MEDICINE ZHEJIANG UNIV
- Filing Date
- 2026-01-30
- Publication Date
- 2026-05-01
AI Technical Summary
Existing hydrogel dressings have limited functionality, poor tissue adhesion, insufficient mechanical properties, difficulty in in-situ molding, and are unable to effectively prevent infection and promote the healing of chronic wounds.
Using modified dermal matrix as raw material, a multifunctional hydrogel is formed by dynamic covalent cross-linking of borate esters. Combining the antibacterial properties of ε-polylysine and the antioxidant and tissue adhesion properties of DHPPA, a shaped hydrogel is prepared that can form in situ on the wound and has self-healing ability.
It achieves seamless adhesion between the hydrogel and the wound, possesses antibacterial, antioxidant, and anti-inflammatory functions, exhibits good biocompatibility and self-healing ability, adapts to the dynamic changes of complex wounds, and reduces secondary damage.
Smart Images
Figure CN121944205A_ABST
Abstract
Description
A multifunctional in-situ repair hydrogel based on modified dermal matrix, its preparation method and application Technical Field
[0001] This invention belongs to the field of biomedical materials technology, and specifically relates to a multifunctional in-situ repair hydrogel based on a modified dermal matrix, its preparation method, and its application. Background Technology
[0002] Wound healing is a complex and dynamic biological process, and effective wound management is crucial for preventing infection, reducing scarring, and accelerating tissue regeneration. An ideal wound dressing should provide a moist healing environment, absorb wound exudate, have good biocompatibility, and effectively prevent external bacterial infection.
[0003] Currently, various natural or synthetic polymer materials have been developed for use in hydrogel dressings, such as hydrogels based on chitosan, collagen, and hyaluronic acid. However, existing hydrogel dressings often have some limitations:
[0004] 1. Limited Function: Most hydrogels only have basic moisturizing and absorption functions and lack active biological activities, such as long-lasting antibacterial, antioxidant or anti-inflammatory capabilities.
[0005] 2. Poor tissue adhesion: Traditional hydrogels have weak adhesion to moist wound tissue and are prone to displacement, requiring secondary dressings (such as tape or bandages) for fixation. This not only increases the complexity of the operation but may also cause secondary damage to newly formed tissue when changing dressings.
[0006] 3. Insufficient mechanical properties: Some hydrogels have low mechanical strength, are easily damaged, and are difficult to adapt to the dynamic changes of moving parts such as joints.
[0007] 4. Limited in-situ molding capability: Pre-formed hydrogels are difficult to perfectly fill deep or complex wounds with irregular shapes, especially for chronic, large-area wounds such as diabetic foot ulcers and burns, resulting in dead space between the dressing and the wound, which affects the healing effect.
[0008] Therefore, developing a hydrogel dressing that can form in situ and possesses excellent tissue adhesion, self-healing ability, and multiple bioactivities such as antibacterial, antioxidant, and anti-inflammatory properties is of great clinical value for the treatment of chronic and infected wounds. Summary of the Invention
[0009] The technical problem to be solved by the present invention is to provide a multifunctional in-situ repair hydrogel based on a modified dermal matrix, its preparation method and application, wherein the hydrogel has good biocompatibility, plasticity and potential self-healing ability.
[0010] This invention provides a multifunctional in-situ repair hydrogel based on a modified dermal matrix. The hydrogel is formed by cross-linking a first polymer precursor and a second polymer precursor through dynamic covalent bonds of borate esters. The first polymer precursor is carboxymethyl chitosan grafted with phenylboronic acid groups and ε-polylysine segments. The second polymer precursor is a soluble decellularized dermal matrix grafted with 3,4-dihydroxyphenylpropionic acid groups after enzymatic hydrolysis.
[0011] This invention also provides a method for preparing a multifunctional in-situ repair hydrogel based on a modified dermal matrix, comprising the following steps:
[0012] (1) Dissolve carboxymethyl chitosan CMCS in a buffer solution; then use EDC / NHS to graft a carboxyl phenylboronic acid compound onto CMCS to obtain CMCS grafted with phenylboronic acid groups; then use EDC / NHS to graft ε-polylysine, and after dialysis and lyophilization, obtain the first polymer precursor;
[0013] (2) The decellularized dermal matrix ADM was enzymatically hydrolyzed in acetic acid solution (pH=3) to obtain a homogeneous and soluble ADM solution; then 3,4-dihydroxyphenylpropionic acid (DHPPA) was grafted onto the collagen / peptide chain in the ADM solution using EDC / NHS, and the second polymer precursor was obtained after dialysis and lyophilization.
[0014] (3) Dissolve the first polymer precursor and the second polymer precursor in physiological buffer solution (such as PBS, pH 7.4) respectively to prepare the first polymer precursor solution and the second polymer precursor solution; mix the two precursor solutions to obtain the hydrogel.
[0015] Preferably, the mass ratio of CMCS, carboxyl-containing phenylboronic acid compound, and ε-polylysine in step (1) is 1:0.1-0.5:0.1-0.5.
[0016] Preferably, the phenylboronic acid compound with a carboxyl group is 4-carboxyphenylboronic acid 4-CPBA.
[0017] Preferably, the mass ratio of ADM to DHPPA in step (2) is 1:0.1-0.3.
[0018] Preferably, the mass concentration of the first polymer precursor solution and the second polymer precursor solution in step (2) is 1-5% w / v.
[0019] Preferably, the mixing of the first polymer precursor solution and the second polymer precursor solution in step (2) is an equal-volume mixing.
[0020] The present invention also provides the application of a multifunctional in-situ repair hydrogel based on a modified dermal matrix in the preparation of biomedical materials for promoting wound healing and possessing antibacterial, antioxidant, anti-inflammatory, or tissue adhesion functions.
[0021] Beneficial effects
[0022] (1) Multifunctional integration: Through ingenious molecular design, the broad-spectrum antibacterial properties of ε-polylysine, the antioxidant and tissue adhesion properties of DHPPA, and the cell growth-promoting properties of ADM are integrated into one system, which also has potential anti-inflammatory effects.
[0023] (2) Excellent tissue adhesion: The introduced catechol group simulates the adhesion mechanism of mussel adhesive protein, enabling the hydrogel to exhibit strong tissue adhesion in a moist wound environment, without the need for secondary fixation, and can effectively close the wound.
[0024] (3) In situ formation and wound adhesion: Hydrogel can be rapidly formed by mixing two precursor solutions. It can be applied to irregular wounds in various ways such as smearing, spraying or injection, achieving seamless adhesion with wound tissue, completely eliminating dead space, and providing the best moist environment for wound healing.
[0025] (4) Dynamic self-healing properties: Based on reversible borate ester crosslinking, the hydrogel network has the potential self-repair ability after being subjected to mechanical damage, which improves its stability and service life as a dressing.
[0026] (5) Good biocompatibility: The main components of the hydrogel (chitosan, collagen, polylysine) are all natural or biocompatible polymers, ensuring the safety of the material. Attached Figure Description
[0027] Figure 1 is a schematic diagram of the hydrogel of the present invention.
[0028] Figure 2 is a schematic diagram of the preparation path of the polymer precursor of the present invention.
[0029] Figure 3 is a schematic diagram of the hydrogel mixing and gelation of the present invention.
[0030] Figure 4 shows the morphology of CMCS-PBA after freeze-drying.
[0031] Figure 5 shows the morphology of the first polymer precursor final product.
[0032] Figure 6 shows the morphology of the viscous liquid after enzymatic hydrolysis of decellularized dermal matrix (10 mg / mL).
[0033] Figure 7 shows the morphology of the second polymer precursor final product.
[0034] Figure 8 shows the rapid gelation morphology of the precursor solution mixture.
[0035] Figure 9 shows the infrared spectrum of the first polymer precursor.
[0036] Figure 10 shows the infrared spectrum of the second polymer precursor.
[0037] Figure 11 shows a cross-sectional microstructure of the freeze-dried hydrogel sample from the example using a scanning electron microscope (SEM).
[0038] Figure 12 shows the rheological properties and macroscopic morphology of the hydrogel in the embodiment, where (A) is the frequency sweep curve of the hydrogel; (B) is the strain sweep curve of the hydrogel; (C) is the step-strain sweep curve of the hydrogel, reflecting its self-healing properties; and (D) is a macroscopic photograph of the hydrogel being stretched and adhered between fingers.
[0039] Figure 13 shows the comprehensive evaluation results of the biocompatibility of the hydrogel in the example. (A) shows the results of the in vitro hemolysis experiment (Hemolysis ratio), comparing the hemolysis rates of the negative control (PBS), positive control (DDW), and hydrogel group; (B) shows the results of the cytotoxicity experiment (CCK-8 method), comparing the cell viability of the blank control group and the hydrogel group.
[0040] Figure 14 shows the in vitro antibacterial properties (inhibition zone) of the hydrogel in the example.
[0041] Figure 15 shows the antioxidant results (DPPH) of the hydrogel in the example.
[0042] Figure 16 shows the in vitro stability and degradation behavior of the hydrogels in the examples. Detailed Implementation
[0043] The present invention will be further illustrated below with reference to specific embodiments. It should be understood that these embodiments are for illustrative purposes only and are not intended to limit the scope of the invention. Furthermore, it should be understood that after reading the teachings of this invention, those skilled in the art can make various alterations or modifications to the invention, and these equivalent forms also fall within the scope defined by the appended claims.
[0044] Example 1
[0045] 1. Preparation of the first polymer precursor (CMCS-PBA-PL)
[0046] ①Preparation of CMCS-PBA:
[0047] Weigh 1.0 g of CMCS and dissolve it in 100 mL of 0.1 M 2-morpholinoethanesulfonic acid MES buffer (pH 5.5). Separately, dissolve 200 mg of 4-carboxyphenylboronic acid (CPBA) in 10 mL of MES buffer, add 280 mg of EDC and 160 mg of NHS, and activate in the dark for 30 minutes. Add the activated solution dropwise to the CMCS solution and react at room temperature for 24 hours. Dialyze the reaction solution to ultrapure water using a MWCO 8-14 kDa dialysis bag for 3 days, and freeze-dry to obtain a white foamy solid CMCS-PBA, as shown in Figure 4.
[0048] ②Preparation of CMCS-PBA-PL:
[0049] Weigh 0.5 g of CMCS-PBA and dissolve it in 50 mL of MES buffer (pH 5.5). Add 120 mg of EDC and 70 mg of NHS, and activate in the dark for 30 minutes. Separately, dissolve 100 mg of ε-PL in 5 mL of MES buffer and add it dropwise to the above solution. React at room temperature for 24 hours. After dialyzing and freeze-drying, the final product CMCS-PBA-PL is obtained, as shown in Figure 5.
[0050] 2. Preparation of the second polymer precursor (ADM-DHPPA)
[0051] ①Standardized enzymatic hydrolysis of ADM:
[0052] 1.0 g of decellularized dermal matrix (ADM) powder was suspended in 100 mL of 0.1 M acetic acid, and 10 mg of pepsin (E / S = 1:100) was added. The mixture was stirred at 20°C for 48 hours. Monitoring with SDS-PAGE and viscosity measurements confirmed that the collagen macromolecules were moderately degraded into soluble components. After the reaction, the pH was adjusted to 7.4 with 0.1 M NaOH at 4°C to inactivate the enzyme, yielding an enzymatically hydrolyzed ADM solution, as shown in Figure 6.
[0053] ② Grafting of DHPPA:
[0054] The enzymatically digested ADM solution was diluted to a protein concentration of 5 mg / mL. Separately, 150 mg of DHPPA was dissolved in 10 mL of MES buffer (pH 5.5), and 200 mg of EDC and 110 mg of NHS were added to activate the solution for 30 minutes. The activated solution was then added dropwise to the ADM solution, and the pH was adjusted to 5.5-6.0. The reaction was allowed to proceed for 24 hours. After dialyzing and freeze-drying, the product ADM-DHPPA was obtained, as shown in Figure 7.
[0055] 3. Formation of hydrogels
[0056] ① Prepare 4% (w / v) PBS (pH 7.4) solutions of CMCS-PBA-PL and ADM-DHPPA respectively.
[0057] ② Equal volumes of the two solutions were rapidly mixed, and a stable hydrogel was formed within 30 seconds at 37°C, as shown in Figure 8. This process simulates the application scenario of co-extruding the two precursor solutions using a dual-barrel syringe, or mixing them immediately before use and applying them to the wound.
[0058] 4. Performance Characterization
[0059] Structural characterization (infrared spectroscopy): To confirm the successful grafting of each functional group, Fourier transform infrared spectroscopy (FTIR) was used to characterize the raw materials and the synthesized polymer precursor.
[0060] Structural confirmation of the first polymer precursor (CMCS-PBA-PL): Figure 9 shows a comparison of the infrared spectra of the raw material carboxymethyl chitosan (CMCS) and the modified precursor (CMCS-PBA-PL). CMCS raw material spectrum: at 3400 cm⁻¹ -1 The vicinity shows broad and strong stretching vibration peaks of -OH and -NH2, at 1600 cm⁻¹. -1 Carboxyl groups (-COO) are visible nearby. - The asymmetric stretching vibration peak of phenylboronic acid (PBA) was observed. The CMCS-PBA-PL product spectrum showed significant changes compared to the starting material. The introduction of PBA was evident in the peak values at 1450-1600 cm⁻¹. -1 A new absorption peak appeared in the region, attributed to the C=C stretching vibration of the benzene ring skeleton; simultaneously, at 1340 cm⁻¹... -1 The characteristic absorption peak of the BO bond was observed nearby, confirming the successful introduction of the phenylboronic acid group. Introduction of ε-polylysine (ε-PL): at 1650 cm⁻¹ -1 (Amide I band) and 1540 cm -1 The absorption peak intensity at the (amide II band) is significantly enhanced, which is attributed to the superposition of the new amide bond (-CONH-) generated by the grafting reaction and the ε-PL peptide chain structure itself. The changes in the above characteristic peaks confirm that phenylboronic acid and ε-polylysine have been successfully grafted onto the carboxymethyl chitosan backbone.
[0061] Structural confirmation of the second polymer precursor (ADM-DHPPA): Figure 10 shows a comparison of the infrared spectra of enzymatically degraded cellular dermal matrix (ADM) and the modified precursor (ADM-DHPPA). ADM raw material spectrum: shows the typical characteristic absorption bands of collagen, including the 3300 cm⁻¹ band. -1 (Amide A band), 3080 cm -1 (Amide B band), 1650 cm -1 (Amide I band), 1550cm -1(Amide II band) and 1240 cm -1 (Amide III band) indicates that the enzymatic hydrolysis process preserved the triple helix structure of collagen. ADM-DHPPA product spectrum: While retaining the above-mentioned collagen characteristic peaks, the spectrum shows the following changes: Introduction of catechol (DHPPA): at 1260 cm⁻¹ -1 The enhanced peak shape in the vicinity is attributed to the CO stretching vibration of the phenolic hydroxyl group; simultaneously, the peak shape at 1400-1600 cm⁻¹ is also enhanced. -1 In the region, the vibrational peaks of the benzene ring skeleton overlapped and broadened with the amide peaks of collagen, indicating the introduction of an aromatic ring structure. Grafting reaction evidence: slight changes in the peak intensity ratio or shape of amide I and amide II bands are consistent with the condensation reaction between the carboxyl group of DHPPA and the amino group of ADM to form a new amide bond. Conclusion: The spectra confirm that 3,4-dihydroxyphenylpropionic acid (DHPPA) has been successfully grafted onto the polypeptide backbone of ADM, endowing the material with a catechol functional group.
[0062] Microscopic Morphology Characterization (SEM): To observe the internal microstructure of the hydrogel, the prepared hydrogel sample was rapidly quenched in liquid nitrogen to fix its structure, followed by freeze-drying. After gold sputtering, its cross-sectional morphology was observed using a scanning electron microscope (SEM). As shown in Figure 11, the prepared hydrogel exhibits a regular, uniform, and highly interconnected three-dimensional porous sponge-like network structure. Pore Size Distribution: Observation shows that the pores inside the hydrogel are uniformly distributed, with a pore size range of approximately 50-100 μm. This micron-sized pore size is very suitable for the adhesion, migration, and inward growth of fibroblasts and keratinocytes. Structural Connectivity: The pores exhibit good connectivity. This open porous structure has the following key technical advantages: High Liquid Absorption Capacity: The large specific surface area endows the dressing with excellent water absorption and retention capacity, effectively absorbing excess exudate from the wound site and maintaining a moist healing environment. Material Exchange Channels: The interconnected channels provide efficient transport channels for oxygen, nutrients, and metabolic waste removal, which is crucial for ensuring the survival of newly formed tissue. Conclusion: SEM results confirmed that the cross-linking of the first polymer precursor and the second polymer precursor formed a structurally complete porous scaffold, providing an ideal physical microenvironment for cell proliferation and tissue regeneration.
[0063] Physical Properties (Rheological Characterization): As shown in Figure 12, rheological tests further revealed the cross-linked network characteristics within the hydrogel. Gel Network Stability (Figure 12A): Frequency scan results show that within the test frequency range (0.1-10Hz), the storage modulus (G') is consistently significantly higher than the loss modulus (G''), indicating that the mixing of the first and second polymer precursors successfully formed a structurally stable elastic gel network. Shear Thinning Properties (Figure 12B): Strain scan results show that the hydrogel exhibits a distinct linear viscoelastic region; as the strain increases (e.g., exceeding 100%), G' rapidly decreases and falls below G'', indicating that the gel network is disrupted and transitions to a sol state. This shear thinning property allows the hydrogel to be smoothly extruded through a syringe and fill irregular wounds. Dynamic Self-Healing Capability (Figure 12C): In alternating high strain (damage) and low strain (recovery) cyclic tests, after the destructive high strain is removed, the hydrogel's G' can rapidly recover to its initial level within seconds, and the recovery rate remains excellent after multiple cycles. This confirms that the reversible recombination mechanism of dynamic borate ester bonds in the system endows the material with rapid self-healing capabilities. Macroscopic adhesion and stretching (Figure 12D): The photographs visually demonstrate the excellent tissue adhesion and extensibility of the hydrogel. As shown, the hydrogel can adhere tightly to the skin surface of the fingers and maintain the connection without breaking during the stretching of two fingers. This property is of great significance for adapting to skin movement at wound sites (especially joints).
[0064] Biocompatibility (ISO 10993): Figure 13 shows the comprehensive evaluation results of the biocompatibility of the hydrogel of this invention. (Figure 13A): The figure shows the comparison of hemolysis rates between the hydrogel group and the negative control (PBS) and positive control (DDW, deionized water). The results show that complete hemolysis (100%) occurred in the positive control group; while the hemolysis rate of the hydrogel group was extremely low (significantly lower than the international standard threshold of 5%), and there was a highly significant statistical difference compared with the positive control group (P<0.0001, marked with ****). This indicates that the hydrogel does not damage red blood cells and has excellent blood compatibility. (Figure 13B): The survival rate of skin fibroblasts after co-culturing with the hydrogel was detected by the CCK-8 assay. The results show that the cell survival rate of the hydrogel group (Hydrogel) was close to 100% compared with the blank control group (Control, set as 100%), and there was no statistically significant difference between the two groups (marked with ns). This indicates that the hydrogel extract has no inhibitory effect on cell growth and no cytotoxicity.
[0065] Based on the above hematological and cytological experimental results, the hydrogel prepared by this invention has good biocompatibility and meets the safety requirements for use as a medical wound dressing.
[0066] Antibacterial Activity: As shown in Figure 14, the inhibitory ability of the hydrogel against representative Gram-positive bacteria (Staphylococcus aureus) and Gram-negative bacteria (Escherichia coli) was visually evaluated using the filter paper / gel sheet diffusion method (zone of inhibition method). The blank control group samples were surrounded by dense bacterial colonies, with no inhibition zones observed, indicating that the control material lacked antibacterial activity. The prepared hydrogel samples all exhibited clear, transparent, and well-defined zones of inhibition. This indicates that the hydrogel can effectively release antibacterial active ingredients, inhibiting the growth and reproduction of surrounding bacteria. This significant antibacterial activity is attributed to the ε-polylysine (ε-PL) grafted into the first polymer precursor. As a natural cationic antimicrobial peptide, ε-PL can disrupt the integrity of bacterial cell membranes through electrostatic interactions, leading to bacterial death. The experimental results confirm that this hydrogel possesses broad-spectrum antibacterial capabilities, effectively preventing bacterial infection at wound sites and providing a sterile environment for wound healing.
[0067] Antioxidant Properties: DPPH free radical scavenging experiments showed that the hydrogel possessed significant free radical scavenging ability, attributed to the catechol structure in DHPPA. As shown in Figure 15, the synthesized final product hydrogel exhibited significant and concentration-dependent antioxidant capacity. The blank control group (Control) showed high absorbance (~1.45) and a deep purple color, indicating that DPPH free radicals were not scavenged. When 0.25 mg / mL of ADM-DHPPA was added, the absorbance decreased to approximately 0.8, and the solution color lightened; when the concentration was increased to 0.5 mg / mL, the absorbance dropped sharply to approximately 0.1, and the solution turned bright yellow, with a scavenging effect comparable to that of the standard antioxidant vitamin C (VC). This confirms that the grafted DHPPA group endows the material with excellent free radical scavenging function. The above results confirm that the DHPPA group grafted onto the ADM backbone successfully retained the redox activity of the catechol structure, endowing the hydrogel with excellent antioxidant function, and is expected to effectively remove excess reactive oxygen species (ROS) from wound sites.
[0068] In vitro stability and degradation behavior characterization: As shown in Figure 16, to evaluate the structural stability of the hydrogel under different liquid environments, the prepared hydrogel samples were immersed in deionized water and phosphate buffered saline (PBS, pH 7.4), and their morphological changes were observed at 37°C. Stability under physiological conditions (PBS group): After immersion in PBS buffer for 24 hours, the hydrogel (right column) still maintained an intact block structure without obvious swelling or disintegration. This indicates that the hydrogel network has good structural stability under physiological saline environment and pH conditions simulating body fluids, and can meet the needs of long-term wound coverage as a wound dressing. Dissociation behavior under low ionic strength (H2O group): In contrast, after immersion in deionized water for 24 hours, the hydrogel (left column) underwent significant structural collapse and dissociation (or excessive swelling leading to structural destruction). This may be due to the lack of ionic strength in deionized water required to maintain the stability of dynamic borate ester bonds, or due to the osmotic pressure difference causing a large number of water molecules to enter the gel network. The experimental results confirm that the hydrogel prepared in this invention has environmental responsiveness. Its excellent stability in physiological buffer ensures its reliability in clinical applications, while its degradable / dissociable properties under specific conditions (such as pure water environment) also suggest that it may have the potential to be easily washed away when changing dressings, which helps to reduce secondary damage to newly formed tissues.
Claims
1. A multifunctional in-situ repair hydrogel based on a modified dermal matrix, characterized in that, The hydrogel is formed by cross-linking a first polymer precursor and a second polymer precursor through dynamic covalent bonds of borate esters; the first polymer precursor is carboxymethyl chitosan grafted with phenylboronic acid groups and ε-polylysine segments; the second polymer precursor is soluble decellularized dermal matrix grafted with 3,4-dihydroxyphenylpropionic acid groups after enzymatic hydrolysis.
2. A method for preparing a multifunctional in-situ repair hydrogel based on a modified dermal matrix, characterized in that, The process includes the following steps: (1) Dissolving carboxymethyl chitosan (CMCS) in a buffer solution; then grafting a carboxyl-containing phenylboronic acid compound onto CMCS using EDC / NHS to obtain CMCS grafted with phenylboronic acid groups; then grafting ε-polylysine onto CMCS again using EDC / NHS, and obtaining the first polymer precursor after dialysis and lyophilization; (2) Enzymatically hydrolyzing decellularized dermal matrix (ADM) in acetic acid solution to obtain a homogeneous and soluble ADM solution; then grafting 3,4-dihydroxyphenylpropionic acid (DHPPA) onto the collagen / peptide chain in the ADM solution using EDC / NHS, and obtaining the second polymer precursor after dialysis and lyophilization; (3) Dissolving the first polymer precursor and the second polymer precursor into physiological buffer solution respectively to prepare the first polymer precursor solution and the second polymer precursor solution; mixing the two precursor solutions to obtain the hydrogel.
3. The preparation method according to claim 2, characterized in that, In step (1), the mass ratio of CMCS, carboxyl-containing phenylboronic acid compound, and ε-polylysine is 1:0.1-0.5:0.1-0.
5.
4. The preparation method according to claim 2 or 3, characterized in that, The phenylboronic acid compound with a carboxyl group is 4-carboxyphenylboronic acid 4-CPBA.
5. The preparation method according to claim 2, characterized in that, The mass ratio of ADM to DHPPA in step (2) is 1:0.1-0.
3.
6. The preparation method according to claim 2, characterized in that, The mass concentrations of the first polymer precursor solution and the second polymer precursor solution in step (2) are 1-5% w / v.
7. The preparation method according to claim 2, characterized in that, In step (2), the mixing of the first polymer precursor solution and the second polymer precursor solution is an equal-volume mixing.
8. The application of a multifunctional in-situ repair hydrogel based on a modified dermal matrix as described in any one of claims 1-7 in the preparation of biomedical materials for promoting wound healing and possessing antibacterial, antioxidant, anti-inflammatory, or tissue adhesion functions.