Composite hydrogel based on extracellular matrix and MXene material as well as preparation method and application of composite hydrogel

Abstract

The invention is applicable to the technical field of biomedical materials, and provides composite hydrogel based on an extracellular matrix and an MXene material as well as a preparation method and application of the composite hydrogel. The composite hydrogel is formed by compounding a human extracellular matrix (hECM) pre-gel solution and a Ti3C2Tx MXene nanosheet dispersion liquid and then carrying out self-assembly gelation, and the excellent rheological property and temperature response type in-situ gelation and injection characteristics of the extracellular matrix (ECM) and the photo-thermal antibacterial and hemostatic enhancement functions of the MXene are integrated. The hemostasis time can be remarkably shortened, the bleeding amount can be reduced, inflammation can be effectively controlled, wound closure is promoted, granulation tissue formation is accelerated, and tissue regeneration is stimulated; tissue residues generated in a clinical operation are converted into functional biological materials, so that resource reutilization is realized; a new scheme is provided for complex wound management, and a new thought is provided for material design in the field of regenerative medicine.

Description

Technical Field

[0001] This invention belongs to the field of biomedical materials technology, and particularly relates to a composite hydrogel based on extracellular matrix and MXene material, its preparation method and application. Background Technology

[0002] Severe bleeding during trauma and surgery is a critical factor endangering patients' lives, especially when high-blood-supply organs such as the liver are damaged. Timely and effective hemostatic intervention is essential for improving patient prognosis. In addition to acute blood loss, complications such as microbial infection, excessive inflammatory response, and impaired tissue repair during wound healing can also significantly aggravate the condition and increase the risk of secondary injury.

[0003] Currently used traditional hemostatic materials in clinical practice, such as fibrin glue, collagen sponges, and synthetic polymers, while possessing certain hemostatic effects, still suffer from insufficient mechanical strength, potential immunogenicity, and limited bioactivity. Furthermore, the complex manufacturing processes of some materials may lead to cytotoxicity, limiting their further clinical application. More critically, most existing hemostatic materials lack intrinsic antibacterial properties, making them ill-suited for the complex treatment needs of infected wounds. Therefore, developing multifunctional integrated biomaterials that combine rapid hemostasis, antibacterial properties, and tissue regeneration promotion has become a crucial clinical need, significantly contributing to improving the healing quality and treatment outcomes of complex wounds.

[0004] Peritumoral tissue, often discarded during traditional tumor resection surgery, has been proven to be a clinically valuable and sustainably usable source of extracellular matrix (ECM). Its biochemical composition is highly similar to normal tissue, allowing it to be processed into functional hydrogels, providing an environmentally friendly and transformative new pathway for biomaterial development. Meanwhile, MXenes, as an emerging class of two-dimensional transition metal carbon / nitrides, show great promise in the biomedical field due to their high specific surface area, excellent electrical conductivity, and efficient photothermal conversion capabilities. Studies have shown that MXene nanosheets can promote rapid aggregation of erythrocytes and platelets, exhibiting significant hemostatic activity. Based on these properties, integrating biomimetic ECM hydrogels with multifunctional MXene materials to construct a novel composite wound dressing is expected to synergistically address multiple clinical challenges such as bleeding control, infection prevention and treatment, and tissue repair, providing a new solution for complex wound management.

[0005] Therefore, this invention proposes a composite hydrogel based on extracellular matrix and MXene material, its preparation method, and its application. Summary of the Invention

[0006] The purpose of this invention is to provide a composite hydrogel based on extracellular matrix and MXene material, its preparation method and application, in order to solve the problems mentioned in the background art.

[0007] The objective of this invention is achieved through the following technical solution:

[0008] A composite hydrogel based on extracellular matrix and MXene material is formed by self-assembly and gelation of a human extracellular matrix pregel solution and an MXene nanosheet dispersion; the human extracellular matrix is ​​derived from discarded liver tissue during tumor resection surgery and prepared after decellularization; the MXene is Ti3C2T x MXene.

[0009] Furthermore, the final concentration of MXene in the composite hydrogel was 25-100 μg / mL.

[0010] Furthermore, the composite hydrogel can gel within 30 minutes at 37 °C through the self-assembly of human extracellular matrix components.

[0011] A method for preparing the composite hydrogel according to the above includes the following steps:

[0012] Step 1: Preparation of human extracellular matrix pregel solution; specifically including: taking liver tissue around the tumor, decellularizing it, degrading residual DNA with deoxyribonuclease I, freeze-drying and grinding it to obtain hECM powder; adding the hECM powder to a hydrochloric acid solution containing pepsin, neutralizing and adjusting it to physiological ionic strength to obtain human extracellular matrix pregel solution;

[0013] Step 2: Preparation of hECM@M composite hydrogel; specifically including: etching Ti3AlC2 powder with hydrofluoric acid, centrifuging and washing, sonicating and low-speed centrifuging, collecting the upper colloidal dispersion, i.e. MXene nanosheet dispersion; mixing human extracellular matrix pregelation solution with MXene nanosheet dispersion, and self-assembling at 37 ℃ for 30 min to form hECM@M composite hydrogel.

[0014] Furthermore, in step 1, the decellularization process includes: cutting the tissue into pieces and placing them in a 1% sodium dodecyl sulfate solution, stirring at 100 rpm for 48 h for preliminary decellularization; then adding 1% Triton-X-100 solution and stirring at 25 ℃ and 100 rpm for 24 h to complete deep decellularization.

[0015] Furthermore, in step 1, the ratio of the mass of hECM powder to the volume of hydrochloric acid solution containing pepsin is 10:1.

[0016] Furthermore, in step 2, the etching conditions are: magnetic stirring at 25 ℃ for 24 h; ultrasonic power not exceeding 100 W, ultrasonic time for 15 min; low-speed centrifugation speed of 1500 rpm, centrifugation time for 10 min.

[0017] An application of the above-mentioned composite hydrogel in the preparation of antibacterial materials, wherein the composite hydrogel has a synergistic antibacterial effect against Staphylococcus aureus and / or Escherichia coli, and the antibacterial effect is enhanced under near-infrared light irradiation.

[0018] An application of the above-mentioned composite hydrogel in the preparation of hemostatic materials, wherein the composite hydrogel achieves hemostasis by activating extrinsic and intrinsic coagulation pathways and enhancing the adhesion ability of erythrocytes and platelets, and the hemostatic effect is improved under near-infrared light irradiation.

[0019] An application of the above-mentioned composite hydrogel in the preparation of skin wound repair materials: the composite hydrogel combined with near-infrared light irradiation can achieve rapid and low-scarring healing of skin wounds.

[0020] Compared with the prior art, the beneficial effects of the present invention are:

[0021] The hECM@M composite hydrogel material prepared in this invention effectively integrates the complementary properties of each component. The ECM matrix, with its excellent rheological properties and temperature-responsive in-situ gelation ability, provides good structural support and smooth injection characteristics; MXene endows the material with therapeutic functions, possessing both highly efficient photothermal antibacterial effects and significantly enhanced hemostatic properties. Therefore, this invention achieves several outstanding advantages:

[0022] (1) The present invention can significantly shorten the hemostasis time and reduce the amount of bleeding, and can also effectively control inflammation, promote wound closure, accelerate the formation of granulation tissue and stimulate tissue regeneration.

[0023] (2) This invention proposes a sustainable strategy, which transforms tissue residues generated during clinical surgery into functional biomaterials, thereby realizing resource reuse.

[0024] (3) This invention highlights the application potential of hECM@M composite hydrogel as a multifunctional treatment platform in complex wound management, and provides new ideas for material design in the field of regenerative medicine. Attached Figure Description

[0025] Figure 1 This is a schematic diagram of the preparation of hECM@M composite hydrogel.

[0026] Figure 2Characterization of hECM@M composite hydrogel (**: p<0.01, highly statistically significant difference; ***: p<0.001, extremely highly statistically significant difference; ****: p<0.0001, extremely statistically significant difference; ns: no statistically significant difference); where: a is a representative decellularized image and histological staining (scale bar: 100 μm), b is a DNA quantification map, c is a TEM image and TEM-EDS elemental map (scale bar: 500 nm), d is a glycosaminoglycan quantification map, and e is a collagen content quantification map.

[0027] Figure 3 The rheological and photothermal properties of the hECM@M composite hydrogel are shown in the figure; where: a is the optical image, b is the shear rate, c is the modulus rheological experiment, d is the temperature-dependent rheological experiment, e is the oscillatory strain experiment, f is the frequency scan curve, g is the temperature rise curve, h is the infrared thermograph, and i is the photothermal statistical evaluation.

[0028] Figure 4 To assess the antibacterial properties and biocompatibility of the hECM@M composite hydrogel; where: a is the antibacterial experiment (scale bar: 100 μm), b is bacterial live / dead staining (scale bar: 100 μm), and c is HDF cell live / dead staining (scale bar: 100 μm).

[0029] Figure 5 The hemostatic effect of hECM@M composite hydrogel on liver injury is shown in the image. Among them, a is an image of a rat liver hemorrhage model, b is the hemostasis time, c is the bleeding volume, d is the prothrombin time, e is the thrombin activation time, f is the erythrocyte adhesion rate, and g is the platelet adhesion rate.

[0030] Figure 6 The image shows the wound healing effect of hECM@M composite hydrogel on a full-thickness skin defect model; where: a is the wound healing image (scale bar: 1 cm), b is H&E staining (scale bar: 100 μm), and c is immunofluorescence staining (scale bar: 100 μm). Detailed Implementation

[0031] To provide a clearer understanding of the technical features, objectives, and beneficial effects of this invention, the technical solution of this invention is described in detail below, but this should not be construed as limiting the scope of implementation of this invention. Unless otherwise specified, the methods used in this invention are conventional methods in this technical field. In this invention, materials, reagents, or instruments whose manufacturers are not specified are all conventional products that can be purchased commercially.

[0032] The specific implementation of the present invention will be described in detail below with reference to specific embodiments.

[0033] Example 1: A method for preparing a composite hydrogel based on extracellular matrix and MXene material;

[0034] Step 1: Preparation of human extracellular matrix (hECM) pregel solution; specifically including:

[0035] Step 1.1: Harvest fresh liver tissue (human-derived) discarded during tumor resection surgery, surrounding the tumor, and cut it into 0.3-0.5 cm pieces. 3 The tissue samples were thoroughly rinsed with phosphate-buffered saline (PBS) to remove blood. The tissue samples were cut into 1-2 mm pieces and placed in 1% sodium dodecyl sulfate (SDS) solution (10 times the volume of the tissue pieces) and stirred at 100 rpm for 48 h for initial decellularization. Subsequently, 1% Triton-X-100 solution (10 times the volume of the tissue pieces) was added, and the mixture was stirred at 25 °C and 100 rpm for 24 h to complete deep decellularization.

[0036] Step 1.2: Rinse the decellularized tissue fragments repeatedly with PBS until no foam is produced to remove residual detergent; then place the tissue fragments in a solution containing 50 U / mL deoxyribonuclease I (DNase I) and treat at 37 °C for 4 h to degrade residual cellular DNA.

[0037] Step 1.3: Rinse tissue fragments three times with PBS for 5 min each time to obtain decellularized human extracellular matrix. Freeze-dry the matrix at -50 °C for 24 h, grind it, and pass it through a 150 μm sieve to collect the fine powder, i.e., hECM powder.

[0038] Step 1.4: First, prepare a 0.01 M hydrochloric acid solution with concentrated hydrochloric acid and deionized water, and verify that its pH is 2; then, under the condition of an ice-water bath at 4 ℃, dissolve 100.0 mg of pepsin powder in the above 0.01 M hydrochloric acid solution, stir at 300 rpm until completely dissolved, and make up to 100.00 mL with 0.01 M hydrochloric acid solution to prepare a 0.01 M hydrochloric acid solution containing 1 mg / mL pepsin. hECM powder was added to a 0.01 M hydrochloric acid solution containing 1 mg / mL pepsin (the ratio of hECM powder mass to the volume of the 0.01 M hydrochloric acid solution containing 1 mg / mL pepsin was 10:1), and digested at room temperature for 48 h to obtain hECM digestion solution. Then, the hECM digestion solution was neutralized with 0.1 M sodium hydroxide and adjusted to physiological ionic strength (ionic strength approximately 0.16 M, pH 7.4) with PBS. The solution was stirred at 150 rpm for 30 min at 4 °C to obtain a homogeneous hECM pregel solution (4% w / v).

[0039] Step 2: Preparation of hECM@M composite hydrogel; specifically including:

[0040] The MXene material used in this step is Ti3C2T. x MXene is prepared by selectively etching the Al layer of the MAX phase precursor Ti3AlC2.

[0041] Step 2.1: Add 1.0 g Ti3AlC2 powder to 20 mL of 28.9 M hydrofluoric acid (HF) solution and stir magnetically at 25°C for 24 h. Then, wash the reaction product multiple times with deionized water at 3500 rpm until the pH of the supernatant stabilizes at neutral (approximately pH 7). Collect the precipitate (i.e., multilayer Ti3C2T). x MXene).

[0042] Step 2.2: Add deionized water to the washed precipitate and sonicate it at low power (power not higher than 100 W) for 15 min; then centrifuge at low speed of 1500 rpm for 10 min and collect the upper dark and uniform colloidal dispersion, i.e. MXene nanosheet dispersion.

[0043] Step 2.3: Take the hECM pregel solution (4% w / v) obtained in step 1.4 and mix it with the MXene nanosheet dispersion. By adjusting the volume of the added MXene nanosheet dispersion, the final concentration of MXene in the final mixed system is 25, 50 and 100 μg / mL, respectively, to obtain composite pregel solutions, denoted as hECM@M1, hECM@M2 and hECM@M3.

[0044] Step 2.4: Before use, store the above composite pregel solution at 4 °C. When using, place the composite pregel solution in a 37 °C environment to allow the hECM components to self-assemble for 30 min, gelling to form a stable, injectable 3D hECM@M composite hydrogel (see schematic diagram for preparation). Figure 1 (As shown).

[0045] Example 2: Characterization of hECM@M composite hydrogel;

[0046] To verify the hECM@M composite hydrogel raw material (hECM and Ti3C2T) x The effectiveness of MXene preparation was verified in this embodiment from three dimensions: macroscopic and microscopic levels, and biochemical quantification. The results are as follows:

[0047] After 48 hours of initial decellularization, the tissue changed from its original yellowish-red color to a transparent white scaffold, macroscopically indicating the removal of cellular components. Histological results further confirmed the decellularization effect: H&E staining (hematoxylin-eosin staining) showed complete disappearance of nuclear structures, while Masson staining indicated that the collagen scaffold structure was intact. DAPI (4',6-diamidin-2-phenylindole) staining did not detect intact nuclei, further confirming the successful removal of nuclear material. Figure 2 (a)

[0048] After a further 24-hour deep decellularization treatment (at which point the decellularization treatment was 72 hours), biochemical quantitative analysis showed that the DNA content significantly decreased to 64 ng / mg after decellularization treatment. Figure 2 (b) meets the general standards for decellularized materials. Meanwhile, the content of glycosaminoglycans (GAG) and collagen content showed no significant loss compared to the original liver tissue. Figure 2 (d and e) indicate that the decellularization process effectively removes cellular components while preserving key extracellular matrix structures and biochemical compositions.

[0049] Transmission electron microscopy (TEM) results showed that the obtained MXene material exhibited a typical thin-layered, sheet-like structure. TEM-EDS analysis further confirmed its elemental composition, primarily consisting of titanium, carbon, and fluorine. Figure 2 c), with Ti3C2T x The expected elemental composition of MXene is consistent, indicating that Ti3C2T x MXene nanosheets have been successfully prepared.

[0050] Example 3: Rheological and photothermal properties of hECM@M composite hydrogel;

[0051] To systematically evaluate the mechanical strength and photothermal response properties of the hECM@M composite hydrogel, this example uses the hECM@M1 (Ti3C2T) prepared in Example 1. x MXene final concentration 25 μg / mL), hECM@M2 (Ti3C2T) x MXene final concentration 50 μg / mL) and hECM@M3 (Ti3C2T) x Three injectable composite hydrogels (MXene final concentration 100 μg / mL) were used as test subjects.

[0052] like Figure 3 As shown in Figure a, all gels remained in a low-viscosity liquid state at 4 °C, and instantly gelled upon heating to 25 °C or 37 °C, fully preserving the temperature response advantage of hECM. Rheological test results show ( Figure 3(b) All gels exhibit typical shear-thinning behavior: viscosity drops sharply as shear rate increases, a property that ensures smooth gel injection.

[0053] Ti3C2T x The introduction of MXene significantly enhances the mechanical properties of the gel. Storage modulus (G) ' (with Ti3C2T) x MXene concentration increases in a stepwise manner with increasing concentrations, among which hECM@M3 G ' The most prominent improvement ( Figure 3 c). Dynamic temperature scan results show ( Figure 3 (d), hECM@M3 in the 4-20 °C range G ' With loss modulus (G) ″ The modulus increases sharply in tandem, remaining stable in the 25-38 °C range, exhibiting high elasticity over a wide temperature range. Cyclic strain experiments further confirm this. Figure 3 In the cases e and f), hECM@M3 exhibits an elastically dominated solid state at low strain (1%), transforms into a viscous-dominated fluid state at high strain (1000%), and the modulus of hECM@M3 is fully recovered after alternating between high and low strain, demonstrating excellent self-healing and structural reversibility, and can withstand the dynamic microenvironment in vivo.

[0054] Photothermal performance test results show that Ti3C2T x MXene imparts strong near-infrared (NIR) absorption to the gel. UV-Vis absorption spectroscopy shows a significant absorption peak at 808 nm for hECM@M3. Figure 3 (g). 808 nm laser (1 W cm⁻¹) -2 After irradiation for 2 minutes, the surface temperature of hECM@M3 jumped to 48.1 °C; after continuous irradiation for 10 minutes, the equilibrium temperatures of hECM, hECM@M1, hECM@M2, and hECM@M3 reached 30.7, 39.3, 49.8, and 61.5 °C, respectively. Infrared thermograms clearly show the concentration-dependent temperature rise of hECM@M1, hECM@M2, and hECM@M3, while hECM only experienced slight temperature fluctuations. Figure 3 (h and i). It is worth noting that hECM@M3 showed the most significant temperature increase under near-infrared irradiation, fully demonstrating its excellent photothermal conversion performance.

[0055] Example 4: Antibacterial properties and biocompatibility of hECM@M composite hydrogel;

[0056] To evaluate the antibacterial properties and biocompatibility of the hECM@M composite hydrogel, this embodiment selected Gram-positive Staphylococcus aureus (S. aureus) and Gram-negative Escherichia coli (E. coli) as representative pathogens (both of which are the most common pathogens in surgical site infections) for analysis.

[0057] The plate colony count results showed that ( Figure 4 (a) Ti3C2T x The introduction of MXene significantly reduced bacterial survival. Compared with the control group (Ctrl, bacterial culture medium only) and the MXene group (Ti3C2T... x Compared to MXene, the hECM@M3 group reduced colony formation; especially under 808 nm laser (1 W cm⁻¹) light. -2 After 10 min of synergistic irradiation, the hECM@M3 group almost completely inhibited bacterial growth, demonstrating a strong synergistic antibacterial ability. Bacterial live / dead staining results further confirmed this trend. Figure 4 (b) In the control group and the Mxene group, the vast majority of bacteria showed green fluorescence (live bacteria), while the proportion of red fluorescence (dead bacteria) increased with increasing MXene concentration. Under near-infrared light illumination, the hECM@M3 group showed almost entirely red fluorescence within the field of view, further confirming its highly efficient bactericidal properties.

[0058] The cell compatibility of the hydrogel was assessed by cell viability staining. Fluorescence microscopy images showed ( Figure 4 (c) Even in the hECM@M3 group with the highest MXene concentration (100 μg / mL), cells co-cultured with the hydrogel maintained high viability, exhibiting dense green fluorescence and almost no red fluorescence signal.

[0059] In summary, hECM@M3 composite hydrogel (Ti3C2T) x MXene (final concentration 100 μg / mL) endows the material with strong antibacterial ability while maintaining excellent biocompatibility, demonstrating its broad potential in biomedical applications.

[0060] Example 5: Hemostatic effect of hECM@M composite hydrogel on liver injury;

[0061] To evaluate the hemostatic properties of the hECM@M composite hydrogel, this embodiment established a rat liver hemorrhage model by inducing acute hemorrhage in the liver using surgical scissors (the rats used in the experiment were purchased from Spiford Biotechnology Co., Ltd.). Figure 5 As shown in Figure a.

[0062] Compared to the control group (Ctrl, treated with PBS), all material treatment groups showed varying degrees of improvement in hemostasis time and bleeding volume. The control group had the longest bleeding duration, while the gelatin group experienced the most severe bleeding. The gelatin sponge group, to some extent, shortened hemostasis time and reduced bleeding volume, consistent with its known clinical hemostatic properties. The hECM, hECM@M3, and hECM@M3+NIR groups further accelerated the hemostasis process and effectively controlled bleeding, with the hECM@M3+NIR group showing the most significant hemostatic effect. Figure 5 (b and c).

[0063] The coagulation function test results showed ( Figure 5 Compared with the control group, the prothrombin time (PT) and partial thromboplastin time (PTT) of all treatment groups were shortened, indicating that both extrinsic and intrinsic coagulation pathways were activated. Furthermore, the hECM@M3 group showed significantly enhanced erythrocyte and platelet adhesion, which was significantly better than the control group, gelatin group, and gelatin sponge group. Figure 5 (fg). This enhanced cell adhesion behavior indicates that hECM interacts with Ti3C2T. x The combined use of MXene synergistically promotes the aggregation and activation of erythrocytes and platelets, resulting in faster and more effective bleeding control.

[0064] In summary, the hECM@M3 composite hydrogel achieves efficient hemostasis by activating extrinsic and intrinsic coagulation pathways and enhancing the adhesion of erythrocytes and platelets; while the hemostatic effect of the hECM@M3+NIR group is further improved under the assistance of near-infrared light, which is significantly better than the hECM@M3 group used alone.

[0065] Example 6: Wound healing effect of hECM@M composite hydrogel on a full-thickness skin defect model;

[0066] To systematically evaluate the therapeutic efficacy of hECM@M composite hydrogel in skin wound healing, this embodiment compares the repair dynamics of different interventions in a rat full-thickness skin defect model. The animal model construction procedure is as follows: skin was removed from the back of rats (the rats used in the experiment were purchased from Spiford Biotechnology Co., Ltd.), and circular wounds with a diameter of 8 mm were prepared.

[0067] like Figure 6As shown in Figure a, the control group (Ctrl, treated with PBS) experienced slow wound contraction and prolonged scab adhesion; the hECM group showed partial premature scab removal and slightly accelerated wound contraction; the hECM@M3 group showed further accelerated healing; and the hECM@M3+NIR group achieved near-complete wound closure by day 9 with minimal scarring, showing a significant difference from the control group. Histological verification of this trend: H&E staining showed that the control group had residual epithelial gaps and disordered granulation structure; the hECM group had thinner epidermis although covered; the hECM@M3 group had thickened granulation tissue and regular dermal arrangement; and the hECM@M3+NIR group had complete epithelial regeneration, nearly normal collagen structure, and the best repair quality. Figure 6 (b)

[0068] To verify the therapeutic effect of hECM@M composite hydrogel on wound healing, immunofluorescence staining was performed to detect angiogenesis markers (CD31), inflammatory markers (TNF-α), and macrophage polarization markers (CD206) in different wound healing groups. The results showed ( Figure 6 c): In CD31 staining, the vascular network in the control group was limited, the density in the hECM group was slightly increased, the hECM@M3 group was significantly improved, and the hECM@M3+NIR group had the richest angiogenesis; in TNF-α staining, the inflammatory signal was highly expressed in the control group, the hECM group could reduce its level, the hECM@M3 group further inhibited the inflammatory response, and the hECM@M3+NIR group had almost no TNF-α positive signal, indicating that its inflammation control effect was the best; in CD206 staining, the control group had only a small number of M2 macrophages, the hECM group promoted polarization, the hECM@M3 group had enhanced effect, and the hECM@M3+NIR group had the highest proportion of CD206⁺ cells.

[0069] In summary, the hECM@M3 composite hydrogel combined with NIR can synergistically promote angiogenesis, inhibit inflammation, and drive macrophage M2 polarization, providing an ideal repair microenvironment for skin wounds and ultimately achieving rapid, low-scarring, high-quality healing.

[0070] The above are merely preferred embodiments of the present invention. It should be noted that those skilled in the art can make several modifications and improvements without departing from the concept of the present invention, and these should also be considered within the scope of protection of the present invention. These modifications and improvements will not affect the effectiveness of the present invention.

Claims

1. A composite hydrogel based on extracellular matrix and MXene material, characterized in that, It is formed by self-assembly and gelation of a pregel solution of human extracellular matrix and a dispersion of MXene nanosheets; the human extracellular matrix is ​​derived from discarded liver tissue during tumor resection surgery and prepared after decellularization; the MXene is Ti3C2T. x MXene.

2. The composite hydrogel according to claim 1, characterized in that, The final concentration of MXene in the composite hydrogel is 25-100 μg / mL.

3. The composite hydrogel according to claim 1, characterized in that, The composite hydrogel can gel within 30 minutes at 37 °C through the self-assembly of human extracellular matrix components.

4. A method for preparing a composite hydrogel according to any one of claims 1-3, characterized in that, Includes the following steps: Step 1: Preparation of human extracellular matrix pregel solution; specifically including: taking liver tissue around the tumor, decellularizing it, degrading residual DNA with deoxyribonuclease I, freeze-drying and grinding it to obtain hECM powder; adding the hECM powder to a hydrochloric acid solution containing pepsin, neutralizing and adjusting it to physiological ionic strength to obtain human extracellular matrix pregel solution; Step 2: Preparation of hECM@M composite hydrogel; specifically including: etching Ti3AlC2 powder with hydrofluoric acid, centrifuging and washing, sonicating and low-speed centrifuging, collecting the upper colloidal dispersion, i.e. MXene nanosheet dispersion; mixing human extracellular matrix pregelation solution with MXene nanosheet dispersion, and self-assembling at 37 ℃ for 30 min to form hECM@M composite hydrogel.

5. The preparation method according to claim 4, characterized in that, In step 1, the decellularization process includes: cutting the tissue into pieces and placing them in a 1% sodium dodecyl sulfate solution, stirring at 100 rpm for 48 h for preliminary decellularization; then adding a 1% Triton-X-100 solution and stirring at 25 ℃ and 100 rpm for 24 h to complete deep decellularization.

6. The preparation method according to claim 4, characterized in that, In step 1, the ratio of the mass of hECM powder to the volume of hydrochloric acid solution containing pepsin is 10:

1.

7. The preparation method according to claim 4, characterized in that, In step 2, the etching conditions are: magnetic stirring at 25 ℃ for 24 h; ultrasonic power not exceeding 100 W, ultrasonic time 15 min; low-speed centrifugation speed of 1500 rpm, centrifugation time 10 min.

8. The application of a composite hydrogel according to any one of claims 1-3 in the preparation of antibacterial materials, characterized in that, The composite hydrogel exhibits synergistic antibacterial activity against Staphylococcus aureus and / or Escherichia coli, and its antibacterial effect is enhanced under near-infrared light irradiation.

9. The application of the composite hydrogel according to any one of claims 1-3 in the preparation of hemostatic materials, characterized in that, The composite hydrogel achieves hemostasis by activating extrinsic and intrinsic coagulation pathways and enhancing the adhesion of erythrocytes and platelets, and its hemostatic effect is enhanced under near-infrared light irradiation.

10. The application of the composite hydrogel according to any one of claims 1-3 in the preparation of skin wound repair materials, characterized in that, The composite hydrogel, when used in conjunction with near-infrared irradiation, can achieve rapid and low-scarring healing of skin wounds.

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