Fiber matrix material for application to wound

Abstract

A nanofiber matrix material for application to a wound, comprising at least one layer of nanofiber. The nanofiber comprises poly-p-dioxanone (PDO), a surfactant, and one or more of the following polymers: poly(lactic-co-glycolic acid) (PLGA), polyglycolic acid (PGA), poly(glycolide-co-caprolactone) (PGCL), poly(lactide-co-caprolactone) (PLCL), polycaprolactone (PCL), polylactic acid (PLA), and poly(4-hydroxybutyric acid) (P4HB). The nanofiber matrix material is easy to prepare and maintains high thermal stability during preparation and use. Moreover, the material is highly hydrophilic; the material can rapidly draw exudate from a wound and help the wound heal faster.

Description

Fiber matrix material applied to wounds Technical Field

[0001] This invention relates to a fibrous matrix material for application to wounds, and more specifically to a highly hydrophilic, biodegradable biomaterial matrix material with good morphological stability that promotes wound healing. Background Technology

[0002] Nanospun fibers, prepared from synthetically biodegradable polymer materials, possess a porous structure and have been widely explored for use in wound dressings. These products promote wound healing and completely degrade within the wound, eliminating the need for dressing changes and preventing secondary trauma. The microporous structure of these products enables effective wound drainage through capillary action, which is crucial for managing wound moisture. Simultaneously, the skeletal structure formed by nanospinning guides cell adhesion, migration, and proliferation, further accelerating wound healing.

[0003] However, most synthetic biodegradable polymers are polyesters. Nanofiber products made from these polymers are typically highly hydrophobic, making it difficult for wound exudate to pass through, resulting in ineffective drainage of fluid and increasing the risk of infection. For example, the internationally marketed product Restrata (Acera Surgical, USA) is composed of independent nanofibers made from two polyester polymers: polylactic acid-glycolic acid copolymer (PLGA) and polydioxanone (PDO). A drawback of this type of product is that due to the hydrophobicity of these synthetic materials, the spun fibers have poor wettability and cannot quickly and effectively drain wound exudate. Furthermore, if current technical solutions include incorporating fibers made from natural hydrophilic materials such as gelatin, collagen, chitosan, and hyaluronic acid into the product, and if the hydrophilic material is spun as a separate layer, this approach only addresses the hydrophilicity of one side of the dressing film, without solving the overall permeability of the product. These hydrophilic fibers lose their mechanical properties after absorbing water. In addition, animal-derived materials may cause immunogenicity.

[0004] Patent application WO2017196325 discloses a method for spinning PLGA and PDO separately to form a tissue substitute that can mimic the extracellular matrix and better heal damaged tissue. However, this invention requires separating the PLGA and PDO materials to form individual spun fibers. Similarly, patent application WO2015116917A1 discloses spinning PLGA and PDO separately to form independent fibers for creating a thermally stable fibrous material. The claims of the related patent (US11739452B) specifically state that PLGA and PDO cannot be mixed.

[0005] The aforementioned patent application involves spinning two fibers separately, forming fibers with independent components. The overall structure of the thermally unstable fiber (PLGA) is stabilized by a thermally stable fiber component (PDO). However, the preparation of such a product is complex, requiring adjustment of the spinning parameters for both fibers. Different polymer materials have different dielectric constants, molecular weights, and other parameters, necessitating different spinning process parameters (voltage, spinning solution delivery rate, receiving distance, etc.) during electrospinning. This makes balancing the two different spun fibers difficult.

[0006] Wound exudate management is crucial for wound healing. If wound exudate cannot be drained from the wound bed in a timely manner and accumulates on the wound, it can lead to infection. While the inventions mentioned above can address the issue of thermal stability, the resulting products lack good hydrophilicity, which can increase the likelihood of wound infection. Although Acera Surgical's Restrata has demonstrated good wound healing capabilities in clinical studies, there are indications that its use increases the risk of wound infection (ClinicalTrials.gov NCT04918784; Foot & Ankle Surgery: Techniques, Reports & Cases 4 (2024) 100362).

[0007] Furthermore, while we cannot be bound by theory, existing evidence suggests that hydrophilic fibers are more conducive to cell adhesion and climbing. The fibers of the extracellular matrix most suitable for cell growth are highly hydrophilic.

[0008] Summary of the Invention

[0009] This invention provides a matrix material composed of nanocomposite fibers with high thermal stability. This matrix material exhibits excellent hydrophilicity and good support, making it suitable as an excellent wound dressing. The matrix material maintains its size and porosity during preparation, storage, and use, while retaining excellent hydrophilicity and the ability to drain wound exudate. The matrix material is completely degradable during use and does not need to be removed from the wound. The hydrophilic fiber structure facilitates cell adhesion and climbing, which is particularly beneficial for wound healing.

[0010] According to one aspect of the present invention, the present invention relates to a fibrous matrix material for application to a wound, comprising at least one nanofiber layer, the nanofiber layer comprising a first composite fiber, wherein the first composite fiber contains a surfactant, at least 20% of poly(p-dioxanone) (PDO), and another polymer in the composite fiber may be one or more of polylactic-co-glycolic acid copolymer (PLGA), polyglycolic acid (PGA), polyglycolic acid-caprolactone copolymer (PGCL), polylactic-co-caprolactone copolymer (PLCL), polycaprolactone (PCL), polylactic acid (PLA), and poly(4-hydroxybutyric acid) (P4HB), and the nanofiber layer does not contain any animal-derived components.

[0011] According to the matrix material of the present invention, the matrix material may further contain one or more other fibers, which may be composed of a single polymer or a composite fiber composed of two or more biodegradable polymers. Furthermore, according to the matrix material of the present invention, regardless of whether the matrix material includes one or more composite fibers, the mass proportion of PDO in the matrix material is at least 20%.

[0012] In the matrix material according to the present invention, the surfactant is a nonionic surfactant.

[0013] According to the matrix material of the present invention, the nonionic surfactant is F68, P407, or Tween.

[0014] According to the matrix material of the present invention, the intrinsic viscosity of PDO is 0.5-3.0 dl / g.

[0015] In the matrix material according to the present invention, the mass content of the surfactant is 0.5%-3%.

[0016] The matrix material according to the present invention contains only one composite fiber, which is composed of a surfactant, PDO and PLGA, wherein the surfactant is F68.

[0017] The matrix material according to the present invention contains composite fibers composed of PDO and PLGA, and also contains a second fiber.

[0018] According to the matrix material of the present invention, at least 70% of the first composite fiber and the second fiber have a fiber diameter between 100 and 4000 nanometers.

[0019] According to the matrix material of the present invention, the nanofiber layer can be completely wetted within 5 seconds when placed in a PBS solution at 25°C.

[0020] According to the matrix material of the present invention, wherein the nanofiber layer is heated at 40°C and the size shrinkage rate is less than 5%.

[0021] In another aspect, the present invention also relates to a method for preparing the matrix material, comprising the following steps:

[0022] (1) Prepare a fiber electrospinning mixture by dissolving the relevant raw materials in a solvent to prepare a spinning solution. (2) Spin the electrospinning mixture into a matrix material by electrospinning.

[0023] The matrix material according to the present invention is used for wound healing.

[0024] The matrix material according to the present invention contains a second fiber in addition to the first composite fiber described herein. The second fiber can be formed by spinning together with the composite fiber, or by spinning the two fibers in layers.

[0025] According to the matrix material of the present invention, the nanofiber layer further comprises a second fiber, the second fiber being composed of one or more of polylactic acid-glycolic acid copolymer (PLGA), polyglycolic acid (PGA), polydioxanone (PDO), polyglycolic acid-caprolactone copolymer (PGCL), polylactic acid-caprolactone copolymer (PLCL), polycaprolactone (PCL), polylactic acid (PLA), and poly4-hydroxybutyric acid (P4HB).

[0026] In another aspect, the invention also relates to a fibrous matrix material for application to a wound, comprising at least one nanofiber layer containing a first composite fiber, the first composite fiber being composed of a surfactant, at least 20% by weight of poly(p-dioxanone) (PDO), and other polymers, said other polymers being one or more of polylactic-co-glycolic acid copolymer (PLGA), polyglycolic acid (PGA), polyglycolic acid-caprolactone copolymer (PGCL), polylactic-co-caprolactone copolymer (PLCL), polycaprolactone (PCL), polylactic acid (PLA), and poly4-hydroxybutyric acid (P4HB), and said nanofiber layer not containing any animal-derived components.

[0027] According to the matrix material of the present invention, the nanofiber layer contains only the first composite fiber.

[0028] According to the matrix material of the present invention, the nanofiber layer contains only the first composite fiber, which is composed of F68, PLGA and PDO with a mass content of at least 20%.

[0029] In another aspect of the present invention, a method for preparing the matrix material according to the present invention comprises the following steps:

[0030] (1) Mix the poly(p-dioxanone) (PDO) constituting the first composite fiber, a surfactant, and one or more other polymers into an organic solvent.

[0031] (2) When a second fiber is present, one or more polymers constituting the second fiber are mixed into an organic solvent;

[0032] (3) The above solution is electrospun into fibers using electrospinning, and the fibers are interwoven in the same fiber layer, accumulating to form a matrix material of a certain thickness; and

[0033] (4) Remove residual organic solvents.

[0034] In another aspect of the invention, the matrix material according to the invention contains two other fibers in addition to the described composite fiber. The additional fiber can be formed by co-spinning and interlacing with the composite fiber, or the two fibers can be spun in layers.

[0035] In another aspect of the invention, the use of the matrix material described in the invention in the preparation of a medicament or dressing for wound healing.

[0036] In another aspect of the invention, a method of using a dressing with the matrix material of the invention is also provided, comprising the following steps: (1) wound cleaning; (2) cutting the dressing to a suitable size according to the size of the wound and applying it to the wound, wherein a small amount of saline may be used to moisten the surface of the dressing, and then a secondary dressing is used to fix it, and it is generally changed every 7-14 days.

[0037] These and other aspects of the invention will become apparent and will be illustrated with reference to the embodiments described below. Attached Figure Description

[0038] Embodiments of the invention will now be described by way of example only, in conjunction with the accompanying drawings, in which:

[0039] Figure 1A shows a SEM image of a fiber layer containing 2% PEG.

[0040] Figure 1B shows a SEM image of a fiber layer containing 5% PEG.

[0041] Figure 1C shows a SEM image of a fiber layer containing 10% PEG.

[0042] Figure 2A shows a SEM image of a composite fiber layer containing 40% PLGA and 60% PDO.

[0043] Figure 2B is a SEM image of a composite fiber layer containing 39% PLGA, 60% PDO, and 1% F68.

[0044] Figure 3 shows a representative photograph of wound healing; the numbers below indicate the number of days post-surgery.

[0045] Figure 4 shows the average healing rate curve of the wound. Detailed Implementation

[0046] For various external and internal wounds, promoting rapid healing is closely related to the wound's microenvironment. For chronic wounds, wound exudate needs to be drained as soon as possible to prevent exudate accumulation and infection.

[0047] This invention reveals that while mixing hydrophilic materials with biodegradable polymers and then spinning them can solve the overall water permeability problem of the product, it leads to a decline in thermal stability. Hydrophilic synthetic materials such as polyethylene glycol (PEG) can be incorporated into fibers to increase their hydrophilicity, but PEG typically requires a certain proportion to alter the hydrophilicity / hydrophobicity of the fiber surface. Excessive PEG content lowers the glass transition temperature of the fiber, severely affecting its thermal stability and consequently impacting the product's water permeability and dimensional stability. The thermal stability of fibers is crucial for the production, storage, and use of the product.

[0048] For example, when hydrophilic polyethylene glycol (PEG) is mixed into biodegradable polymer materials alone, as shown in Figure 1A (2% PEG), Figure 1B (5% PEG) and Figure 1C (10% PEG), it can be seen that a small amount of PEG does not significantly improve the hydrophilicity of the product. On the other hand, increasing the amount of PEG may lead to a decrease in the glass transition temperature of the product, which in turn causes the product to soften during heating, resulting in a decrease in the porosity of the product, making the film transparent or even completely eliminating the porosity.

[0049] When a water droplet comes into contact with a polymer surface, a contact angle of less than 90 degrees indicates hydrophilicity; when a water droplet comes into contact with a polymer surface, a contact angle of greater than 90 degrees indicates hydrophobicity.

[0050] Through experimentation, this invention designs a matrix material that can be used to prepare an ideal wound-healing product. This material firstly rapidly infiltrates within seconds and secondarily exhibits excellent thermal stability, without shrinking during heating. Therefore, this invention provides a fibrous matrix material with high thermal stability, which also possesses hydrophilicity and good support, maintaining porosity for better drainage of wound exudate.

[0051] The matrix material of this invention employs a composite fiber made by adding a certain amount of PDO and a small amount of surfactant to the fiber material, thereby simultaneously solving the problems of thermal stability and hydrophilicity. Other components include biodegradable polymers, such as polylactic-co-glycolic acid copolymer (PLGA), polyglycolic acid-caprolactone copolymer (PGCL), polyglycolic acid (PGA), polylactic-co-caprolactone copolymer (PLCL), polycaprolactone (PCL), polylactic acid (PLA), poly4-hydroxybutyric acid (P4HB), polyhydroxyalkanoates (PHA), etc., or one or more of them.

[0052] In a PLGA, the molar ratio of L to G can be from 90:10 to 10:90.

[0053] The molar ratio of G to CL in PGCL can be from 90:10 to 10:90.

[0054] The molar ratio of L to CL in PLCL can be from 90:10 to 10:90.

[0055] PLA can be dextrorotatory polylactic acid (PDLA), levorotatory polylactic acid (PLLA), or racemic polylactic acid (PDLLA).

[0056] One or more of the above polymers are mixed with polydioxanone (PDO) and a surfactant in an organic solvent, and then electrospun to form composite fibers.

[0057] Composite fibers are fibers formed by mixing two or more polymer materials. These two polymer materials are dissolved and mixed uniformly in a solvent in a certain proportion, and together form the fiber during spinning. Monocomponent fibers are fibers formed from a single polymer material.

[0058] Both composite fibers and single-component fibers can contain surfactants. The matrix material can be composed of one type of composite fiber, or it can be composed of composite fibers and one or more other composite fibers or single-component fibers.

[0059] The PDO content in the composite fiber is at least 20%, but can be 25%, 30%, 35%, 40%, 45%, 50%, 55%, 60%, 70%, or 80%.

[0060] The matrix material of this invention also includes a composite fiber containing PDO and another fiber. The other fiber can be a single-component fiber composed of one of the aforementioned biodegradable polymers, or a composite fiber containing different mass ratios of PDO. This fiber may contain a surfactant.

[0061] The matrix material of this invention also includes a composite fiber containing PDO and two other fibers. The other two fibers can be single-component fibers composed of one of the aforementioned biodegradable polymers, or composite fibers containing different mass ratios of PDO. Both fibers can contain surfactants.

[0062] This invention prepares nanofiber membranes through a more rational structural design and material selection. By adding appropriate additives, such as surfactants, to hydrophobic and biodegradable polymers, the hydrophilicity of the dressing of this invention is greatly improved, promoting wound healing. The added surfactants can be cationic, anionic, or nonionic surfactants, preferably nonionic surfactants, such as polyoxyethylene-polyoxypropylene ether block copolymers, for example: Poloxamer 188 (i.e., F68) and P407 (also known as Poloxamer 407). Combinations of these additives can be added; some combinations can achieve complete wetting within seconds (e.g., the results in Table 1), helping to rapidly drain wound exudate. Wetting tests can be performed in PBS solution at 25°C. The surfactant content in the fibers is generally 0.5%-3%, for example, 0.8%, 1%, 1.2%, 1.5%, 1.7%, 2%, 2.2%, 2.5%, 2.7%.

[0063] F68, also known as poloxamer 188, H(C2H4O) a (C3H6O) b (C2H4O) a OH, ethylene oxide unit (a) is 75-85, propylene oxide unit (b) is 25-30, CAS No.: 691397-13-4, Manufacturer: BASF.

[0064] P407, also known as poloxamer 407, H(C2H4O) a (C3H6O) b (C2H4O) a OH, ethylene oxide unit (a) is 95-105, propylene oxide unit (b) is 54-60, CAS No.: 9003-11-6, Manufacturer: BASF.

[0065] The diameter of all or most of the fibers, for example, at least 60%, at least 70%, at least 80% by weight, is between 100 and 4000 nanometers, preferably between 200 and 2000 nanometers, more preferably between 400 and 1000 nanometers, for example around 500, 600, 700, 800, or 900 nanometers.

[0066] Electrospinning is a highly efficient spinning and film-forming process used to prepare fibrous polymer membranes with fiber diameters ranging from nanometers to micrometers. Electrospinning methods typically use a high-voltage electric field to inject a current of a specific polarity into a polymer solution / melt, causing the solution / melt to be accelerated and sprayed towards a collection surface of opposite polarity, thereby forming solid fibers. The relative motion between the nozzle and the collection surface can form a fiber layer. The fiber matrix formed by electrospinning has a three-dimensional porous structure with a relatively large surface area. Good fiber formation requires optimization of solution parameters and electrospinning configuration. Controllable parameters during the electrospinning process affect the fiber diameter and the drug release pattern from the membrane matrix. In this way, the electrospinned membrane matrix can be customized to achieve the desired drug release pattern. The polymers used for electrospinning described above are mixed in solution form, and a voltage from about 5-30 kV, preferably 10-25 kV, and more preferably 11-20 kV can be applied to form fibers. Electrospinning uses two or more electrospinning solutions to form fibers, which are then mixed and interwoven in the same fiber layer, accumulating to form a matrix material with a certain thickness, such as 0.01-1 mm.

[0067] The organic solvent can be one or more of hexafluoroisopropanol, trifluoroethanol, dichloromethane, chloroform, etc.

[0068] When using dressings with the matrix material of this invention, first clean the wound, then cut the dressing to a suitable size according to the wound size and apply it to the wound. A small amount of saline solution can be used to moisten the surface of the dressing; then, a secondary dressing is used for fixation. Generally, the dressing should be changed every 7-14 days.

[0069] Example 1

[0070] The hydrophilic polymer polyethylene glycol (PEG) was mixed into the biodegradable polymer material PLGA (50-50). The material ratios were as follows: Group 1: 98% PLGA + 2% PEG; Group 2: 95% PLGA + 5% PEG; Group 3: 90% PLGA + 10% PEG.

[0071] Electrospinning was performed using a positive voltage of 10-20kV, a negative voltage of 2-8kV, a roller speed of 50rpm, and a flow rate of 4-10ml / hour. After heating in an oven at 40℃ for 24 hours, the product was observed using a scanning electron microscope.

[0072] Heat shrinkage % is calculated as the rate of area reduction before and after heating: (area before heating - area after heating) / area before heating × 100%.

[0073] Referring to Figure 1A (Group 1, 2% PEG), Figure 1B (Group 2, 5% PEG), and Figure 1C (Group 3, 10% PEG), it can be seen that the porosity gradually decreases, and in Group 3 it almost disappears. A small amount of PEG cannot significantly improve the hydrophilicity of the product, while increasing the amount of PEG may lead to a decrease in the glass transition temperature of the product, causing the product to soften during heating, which in turn leads to a decrease in the porosity of the product, and the film becomes transparent or even disappears.

[0074] Example 2

[0075] Taking experimental group 8 as an example, PLGA (50 / 50), PDO and F68 were added to a glass bottle according to the mass ratio in Table 1. Hexafluoroisopropanol (HFIP) was added and stirred on a magnetic stirrer until it was transparent and free of impurities. Then it was added to a disposable syringe to prepare spinning solution A.

[0076] Place spinning solution A on the feed pump of the electrospinning machine and begin electrostatic blending. Positive voltage: 10-20kV; negative voltage: 2-8kV; roller speed: 50rpm; flow rate: 4-10ml / hour.

[0077] Table 1: Fiber content and immersion time test results for various samples

[0078] The experimental data show that incorporating PDO into the fibers improves the thermal stability of the matrix material, resulting in a lower shrinkage rate after heating. Adding PDO increases the hydrophilicity of the matrix material, leading to a shorter wetting time. However, adding a small amount of F68 further improves wettability and enhances thermal stability. While we cannot be bound by theory, adding F68 allows for better crystallization of the polymer, achieving a stable state. Simultaneously, due to the relatively small molecular weight of F68, it migrates more easily to the fiber surface during drying and heating, significantly increasing the fiber's hydrophilicity. Adding a small amount of F68 can improve both the fiber's hydrophilicity and the thermal stability of the matrix material. The samples obtained from experimental groups 6 and 13 were observed under a scanning electron microscope (SEM), and the results are shown in Figures 2A and 2B. The figures show that the matrix fibers are well separated after heating, maintaining high porosity, and the fiber fusion observed in examples (1A, 1B, 1C) is not observed. This indicates that the fibers in these samples maintain good hydrophilicity while also possessing excellent thermal stability.

[0079] Example 3

[0080] Similarly, the matrix material can be composed of one or more fibers other than the composite fiber. The first fiber (fiber A) can be a composite fiber composed of PLGA, PDO, and F68, and the second fiber (fiber B) can be composed of a single polymer or another composite fiber. The following example illustrates an embodiment of preparing a matrix material from a composite first fiber and a second fiber of another polymer.

[0081] Add PLGA, F68, and PDO to a glass bottle according to the mass ratio in Table 2. Add HFIP and stir on a magnetic stirrer until the mixture is transparent and free of impurities. Then add the mixture to a disposable syringe to prepare spinning solution A.

[0082] Another polymer was added to a glass bottle according to the mass ratio in Table 2. HFIP was added and stirred on a magnetic stirrer until it became transparent and free of impurities. Then it was added to a disposable syringe to prepare spinning solution B.

[0083] Place spinning solutions A and B on the feed pump of the electrospinning machine respectively, and begin electrostatic blending. The positive voltage is 10-20 kV, the negative voltage is 2-8 kV, and the drum speed is 200 rpm; the flow rate of the spinning solution is 4-10 ml / hour. Adjusting the feed rate of the spinning solution according to the dry matter concentrations in solutions A and B will maintain a dry matter ratio of PDO-containing composite fiber A to fiber B of approximately 1:1.

[0084] Table 2: The ratio of A fibers to B fibers in various samples, and the results of the immersion time test.

[0085] As can be seen, composite fibers can be combined with one or more other fibers to form a matrix material. As long as the mass ratio of PDO in the matrix material exceeds 20% and the mass ratio of surfactant (such as F68) is greater than 0.5%, the matrix material has good thermal stability and hydrophilicity, making it very suitable for use as a wound growth matrix.

[0086] Example 4

[0087] The wound healing ability of the matrix material prepared in experimental group 13 of Example 2 was tested in a full-skin defect model of a miniature Bama Xiang pig. Four miniature Bama Xiang pigs underwent full-skin wounds on their backs, five wounds per pig. The matrix material prepared in the protocol was applied directly to the wounds. A secondary dressing with exudate absorption function was then applied. Representative images of the wounds are shown in Figure 3. The wound size was recorded every seven days; Figure 3 shows days 0, 7, 14, 21, and 28 from left to right. The wound healing rate was calculated based on the change in wound area.

[0088] As shown in Figure 3, due to the excellent hydrophilicity of the matrix material prepared in this invention, the tissue fluid from the wound can rapidly infiltrate the matrix material, and no dimensional changes occur after contact with the wound exudate, demonstrating good stability. During the wound healing process, there is no excessive accumulation of exudate, and no wound infection occurs.

[0089] The wound healing rate is shown in Figure 4. This matrix material can rapidly promote wound healing without the risk of infection.

[0090] Those skilled in the art will understand that various components / parts of the products, formulations, apparatuses, methods, systems, and embodiments described in this application may be modified (added and / or removed) without departing from the full scope and spirit of the invention, and such modifications are covered by the scope and spirit of the invention.

Claims

1. A fibrous matrix material for application to a wound, comprising at least one nanofiber layer, the nanofiber layer containing a first composite fiber, the first composite fiber comprising one or more of poly(p-dioxanone), a surfactant, and other polymers, the other polymers including polylactic acid-glycolic acid copolymer, polyglycolic acid, polyglycolic acid-caprolactone copolymer, polylactic acid-caprolactone copolymer, polycaprolactone, polylactic acid, and poly4-hydroxybutyric acid, wherein the poly(p-dioxanone) contains at least 20% by mass of the fiber, and The nanofiber layer does not contain any animal-derived components.

2. The matrix material of claim 1, wherein the surfactant is a nonionic surfactant.

3. The matrix material of claim 2, wherein the nonionic surfactant is F68, P407 or Tween.

4. The matrix material of claim 1, wherein the surfactant in the first composite fiber has a mass content of 0.5%-3%.

5. The matrix material of claim 1, wherein at least 70% of the first composite fibers have a diameter between 100 and 4000 nanometers.

6. The matrix material of claim 1, wherein the nanofiber layer is fully wetted within 5 seconds when placed in a PBS solution at 25°C.

7. The matrix material of claim 1, wherein the nanofiber layer contains a second fiber, the second fiber being composed of one or more of polylactic acid-glycolic acid copolymer, polyglycolic acid, polydioxanone, polyglycolic acid-caprolactone copolymer, polylactic acid-caprolactone copolymer, polycaprolactone, polylactic acid, and poly4-hydroxybutyric acid.

8. A method for preparing the matrix material of claim 1 or 7, comprising the following steps: (1) Mix the poly(p-dioxanone) (PDO), surfactant and one or more other polymers that make up the first composite fiber into an organic solvent; (2) When a second fiber is present, one or more polymers constituting the second fiber are mixed into an organic solvent; (3) The above solution is electrospun into fibers using electrospinning, and the fibers are interwoven in the same fiber layer, accumulating to form a matrix material of a certain thickness; and (4) Remove residual organic solvents.

9. Use of the matrix material of any one of claims 1-7 in the preparation of a medicament or dressing for wound healing.

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