A surface nano-coating anti-adhesion material for sacral nerve cyst wrapping

Abstract

The application discloses a surface nano-coating anti-adhesion material for sacral cistema cyst wrapping, and relates to the field of biomaterials, which comprises a sheet-shaped base material layer for wrapping a sacral cistema cyst, and a surface functional coating combined with at least one surface of the base material layer; the surface functional coating is a nano-coating which is configured to inhibit fibroblast adhesion through a physical barrier and a biological activity regulation dual mechanism; the anti-adhesion material is constructed by building a multifunctional nano-coating on the surface of an existing base material, the coating can effectively inhibit the initial adhesion and subsequent activation and proliferation of fibroblasts, significantly reduce the deposition of collagen fibers at the material-nerve interface, thereby preventing the formation of postoperative adhesions, greatly improving the long-term curative effect and safety of the wrapping operation, and completely retaining the original mechanical strength and surgical operability of the base material.

Description

Technical Field

[0001] This invention relates to biomaterials technology, specifically to a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery. Background Technology

[0002] Sacral canal cysts are dilatational lesions occurring in the sacral nerve root sleeves. Some symptomatic cysts can cause severe radiating pain in the lower extremities, sensory abnormalities, and bowel and bladder dysfunction. In recent years, a minimally invasive surgical technique called "wrapping surgery" has proven to be an effective method for treating symptomatic sacral canal cysts (see reference:

[0003] Sugawara T, et al. Novel wrapping surgery for symptomatic sacral perineural cysts. J Neurosurg Spine. 2022. The core of this procedure is to separate the cyst from the surrounding nerve roots and then wrap and fix it with a biocompatible material (such as expanded polytetrafluoroethylene membrane) to physically limit the cyst's re-expansion, thereby relieving pressure on adjacent nerve roots.

[0004] However, this advanced surgical technique faces a long-standing and unresolved clinical challenge: postoperative adhesion between the implanted material and adjacent nerve roots and the dural sac. Currently used wrapping materials, such as e-PTFE membranes or sutureable artificial dura maters, are designed primarily to provide a mechanical barrier and meet surgical operability requirements, without specifically addressing anti-adhesion functions. When these materials are implanted as foreign bodies into the narrow sacral canal, they trigger a foreign body response and repair process in the host. During this process, fibroblasts readily adhere to the material surface, proliferate, and excessively secrete collagen, ultimately forming dense fibrous scar tissue that firmly adheres the wrapping material to the adjacent nerve roots.

[0005] Such adhesions can restrict the normal physiological gliding of nerve roots, potentially leading to "adhesive radiculopathy" months or even years post-surgery. This manifests as recurrent pain, limb numbness or weakness, severely impacting the long-term efficacy of the surgery and the patient's quality of life. It is also one of the causes of "failed spinal surgery syndrome (FBSS)." Although liquid anti-adhesion agents (such as hyaluronic acid and chitosan) have been used clinically, they are easily diluted, displaced, or absorbed too quickly in the dynamic environment of cerebrospinal fluid flushing and tissue activity, making it difficult to provide a durable and stable barrier.

[0006] In summary, existing wrapping materials have inherent defects in their anti-adhesion function. There is a lack of a dedicated material that can adapt to the depth of the wrapping procedure, maintain excellent surgical performance, and actively and persistently inhibit fibrotic adhesions. Solving the postoperative adhesion problem is an urgent clinical need to improve the long-term success rate of sacral canal cyst wrapping surgery, and it is also the core technical problem that this invention aims to solve. Summary of the Invention

[0007] The purpose of this invention is to provide a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery. It is suitable for effectively wrapping the cyst during sacral canal cyst wrapping surgery and preventing postoperative adhesion between the implanted material and adjacent nerve roots and dural sac, thereby improving the long-term efficacy and safety of the surgery and solving the problem that existing sacral canal cyst wrapping materials are prone to fibrosis and adhesion to nerve roots after surgery.

[0008] To achieve the above objectives, the present invention provides the following technical solution:

[0009] In a first aspect, the present invention provides a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery, comprising:

[0010] A sheet-like base material layer is used to wrap the sacral canal cyst;

[0011] And a surface functional coating bonded to at least one surface of the substrate material layer;

[0012] The surface functional coating is a nano-coating, which is configured to inhibit fibroblast adhesion through a dual mechanism of physical barrier and bioactivity regulation.

[0013] Specifically, its anti-adhesion mechanism is reflected in the following three aspects:

[0014] 1. Initial antifouling layer formation: The PLGA matrix and drug-loaded PLGA nanoparticles form a continuous and dense nanoscale film on the e-PTFE surface. In the body fluid environment, the hydrophilic / hydrophobic balance of this film can greatly reduce the adsorption of non-specific proteins (such as fibrinogen and fibronectin), thereby weakening the protein "intermediary" layer on which fibroblast adhesion depends from the source.

[0015] 2. Spatiotemporal controlled drug release intervention in the inflammation-fibrosis cascade: Drug-loaded nanoparticles dispersed in the coating act as miniature "drug warehouses," releasing dexamethasone slowly and continuously with near-zero order kinetics as the PLGA matrix gradually degrades. The drug reaches an effective concentration locally, precisely targeting key cells in adhesion formation—macrophages and fibroblasts. Dexamethasone regulates the trauma microenvironment from a pro-fibrotic "M1" macrophage-dominated state to a tissue-repair-promoting "M2" state by inhibiting the expression of pro-inflammatory factors (such as TNF-α and IL-1β) and pro-fibrotic factors (such as TGF-β1), and directly inhibits the transformation of fibroblasts into highly secretory myofibroblasts.

[0016] 3. The lasting protective effect of the physical barrier: Even after the drug is completely released, the residual structure of the PLGA coating that has not been completely degraded, as well as its firm interface with the substrate material, can still act as a physical barrier, continuously preventing the migration of fibroblasts and their direct contact with the material surface. This step-by-step, synergistic defense system, consisting of anti-protein adsorption, drug intervention signaling pathways, and lasting physical isolation, is the fundamental guarantee for the long-term anti-adhesion effect of this invention.

[0017] Furthermore, the base material layer is a stitchable artificial diaphragm or an expanded polytetrafluoroethylene (ePTFE) membrane.

[0018] Furthermore, the surface functional coating is composed of a biocompatible polymer matrix and nano-functional components dispersed in the polymer matrix.

[0019] Furthermore, the polymer matrix is ​​selected from one or more of polyethylene glycol and its derivatives, phospholipid polymers, and polylactic acid-glycolic acid copolymers.

[0020] Furthermore, the nanofunctional component is at least one of drug-loaded nanoparticles, bioactive nanoparticles, and surface topological structure nanounits.

[0021] Furthermore, the drug-loaded nanoparticles are loaded with anti-inflammatory or anti-fibrotic drugs, wherein the anti-inflammatory drug is dexamethasone or methylprednisolone; and the anti-fibrotic drug is mitomycin C or 5-fluorouracil.

[0022] Furthermore, the bioactive nanoparticles are selected from nano-hydroxyapatite or mesoporous silica nanoparticles.

[0023] Furthermore, the surface topology nanounits are arrays of nanopillars or nanopits formed on the coating surface.

[0024] Furthermore, the thickness of the surface functional coating is 50 nanometers to 5 micrometers.

[0025] Secondly, the present invention provides a method for preparing a surface nano-coating anti-adhesion material as described above, comprising the following steps: preparing a coating solution containing a polymer matrix and nano-functional components; forming a surface functional coating on the surface of a substrate material using a dip-coating-coating method, a spraying method, an electrospinning method, or a layer-by-layer self-assembly method; and obtaining the material after drying or cross-linking curing.

[0026] Compared with existing technologies, the present invention provides a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery. By constructing a multifunctional nano-coating on the surface of existing base materials (such as artificial dura mater or e-PTFE membrane), it provides a dual anti-adhesion mechanism combining passive physical barrier and active biological regulation. This coating can effectively inhibit the initial adhesion and subsequent activation and proliferation of fibroblasts, significantly reduce the deposition of collagen fibers at the material-nerve interface, thereby preventing the formation of postoperative adhesions, greatly improving the long-term efficacy and safety of wrapping surgery, while retaining the original mechanical strength and surgical operability of the base material. Attached Figure Description

[0027] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0028] Figure 1 This is a schematic diagram of the overall structure provided for an embodiment of the present invention.

[0029] Explanation of reference numerals in the attached figures:

[0030] 1. Base material layer; 2. Surface functional coating. Detailed Implementation

[0031] To enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0032] As attached Figure 1 As shown:

[0033] Example 1:

[0034] This invention provides a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery, comprising:

[0035] Substrate material layer 1: In this embodiment, expanded polytetrafluoroethylene (e-PTFE) membrane (thickness approximately 0.1 mm, porosity approximately 70%) is selected. The e-PTFE membrane is chosen because it has good biocompatibility, stable physicochemical properties and excellent suture / clampability, which can firmly encapsulate the cyst and provide physical isolation.

[0036] Surface functional coating 2: A nano-coating bonded to one side of the e-PTFE membrane (i.e. the side facing the nerve root during surgery).

[0037] Polymer matrix: Polylactic acid-glycolic acid copolymer (PLGA, LA:GA=75:25) was selected. PLGA has good biocompatibility and controllable degradation, and its degradation cycle can be adjusted by the copolymerization ratio, making it suitable as a drug sustained-release carrier.

[0038] The functional nanocomponent is a drug-loaded nanoparticle. Specifically, it consists of PLGA nanoparticles loaded with the anti-inflammatory drug dexamethasone. These nanoparticles were prepared via an emulsification-solvent evaporation method, with an average particle size of approximately 200 nanometers and a drug loading rate of approximately 10 wt%.

[0039] Coating structure: It is a single-layer uniform composite coating. A continuous film is formed with PLGA matrix, in which PLGA nanoparticles loaded with dexamethasone are uniformly dispersed.

[0040] A method for preparing a surface nano-coating anti-adhesion material as described above includes the following steps:

[0041] Preparation of coating solution: Dissolve PLGA (75:25) in dichloromethane to prepare a 5% (w / w) solution. Disperse PLGA nanoparticles loaded with dexamethasone in this solution and sonicate to ensure uniform dispersion, forming a coating dispersion.

[0042] Substrate pretreatment: The e-PTFE membrane is cut to the required size, cleaned with ethanol and vacuum dried to remove surface contaminants.

[0043] Coating formation: The dip-coating-coating method is used. The pretreated e-PTFE membrane is vertically immersed in the above coating dispersion, held for 10 seconds, and then pulled out of the liquid surface at a constant speed (2 mm / s) to form a uniform liquid film on its surface. If the speed is too slow (<1 mm / s), the coating will be too thick, prone to cracking, and affect the flexibility of the substrate; if the speed is too fast (>5 mm / s), the coating will be too thin and uneven, and may not be able to form a continuous barrier. The preferred lifting speed range is 1.5-3 mm / s, within which a uniform coating with a thickness of 1-2 micrometers and good adhesion can be obtained.

[0044] Drying and Curing: The coated membrane was placed in a fume hood and dried at room temperature for 1 hour to allow the solvent to evaporate. It was then transferred to a vacuum drying oven and dried further at 40°C for 24 hours to cure the PLGA matrix and firmly bond it to the e-PTFE membrane surface through physical adsorption and partial permeation into the micropores. Temperatures below 30°C may result in solvent residue and an unstable coating; temperatures above 50°C may cause drug degradation or excessively rapid denaturation of PLGA. 40°C is a balance point, ensuring sufficient solvent evaporation and moderate matrix curing to provide initial strength without compromising drug activity. 24 hours of vacuum drying helps form a dense microstructure, delaying the initial burst release of the drug.

[0045] Finished product: An anti-adhesion e-PTFE membrane with a nano-coating on the surface was obtained. The coating thickness was measured to be approximately 1.5 micrometers.

[0046] Working principle: After implantation, the PLGA matrix slowly degrades in body fluids. The drug-loaded PLGA nanoparticles dispersed within it subsequently release dexamethasone. The drug is released locally and continuously at a controlled rate, effectively inhibiting acute inflammatory responses induced by surgical trauma and excessive activation and proliferation of fibroblasts. Simultaneously, the intact PLGA coating itself constitutes a physical barrier, passively blocking non-specific adhesion of proteins and cells in the initial stage. This synergistic effect of the dual mechanism of "physical barrier + sustained drug release" fundamentally reduces collagen fiber deposition at the material-nerve interface.

[0047] This embodiment is particularly suitable for cases where the risk of adhesion is assessed as high during surgery (such as thin cyst walls, tight adhesion to nerve roots, or large dissection wounds). Locally released dexamethasone provides potent anti-inflammatory effects while avoiding the side effects of systemic administration, achieving targeted and long-lasting anti-adhesion treatment.

[0048] Example 2:

[0049] This invention provides a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery, comprising:

[0050] Base material layer 1: In this embodiment, a sutureable artificial dura mater (a porous patch composed of interwoven collagen fibers) is selected. The artificial dura mater is chosen because it has excellent biocompatibility with human dura mater tissue and is easy to suture and fix during surgery.

[0051] Surface functional coating 2: Nano-coatings bonded to one side of the artificial hard membrane.

[0052] Polymer matrix: A blend of polyethylene glycol (PEG) and phospholipid polymers is selected. This mixture can form a highly hydrophilic "hydration layer," making it an excellent anti-protein adhesion material.

[0053] The nanofunctional component is mesoporous silica nanoparticles. These nanoparticles are approximately 100 nanometers in diameter, have a regular mesoporous structure, and a large specific surface area.

[0054] Coating structure: It is a two-layer structure. The layer closest to the substrate is a thin layer rich in phospholipids to enhance the binding force with the collagen substrate; the outer layer is a composite layer of PEG and mesoporous silica nanoparticles.

[0055] A method for preparing a surface nano-coating anti-adhesion material as described above includes the following steps:

[0056] Preparation of coating solutions: The inner layer solution is an ethanol solution of phospholipids; the outer layer solution is an aqueous solution of PEG and aminated mesoporous silica nanoparticles.

[0057] Substrate pretreatment: Artificial dura mater was wetted with phosphate-buffered saline (PBS).

[0058] Coating formation: Layer-by-layer self-assembly (LBL) technology is used.

[0059] First, the artificial dura mater is immersed in the inner layer solution to adsorb a layer of phospholipid molecules, and then removed and dried.

[0060] Then, it is immersed in the outer solution, and through electrostatic interactions, PEG molecules and positively charged aminated silica nanoparticles are adsorbed onto the negatively charged phospholipid layer.

[0061] The above steps can be repeated 3-5 times to control the coating thickness and nanoparticle density.

[0062] Crosslinking and curing: Genipin is used as a crosslinking agent to gently crosslink the assembled coating to enhance its stability in the water environment.

[0063] Finished product: An anti-adhesion artificial hard membrane with a bioactive nano-coating on the surface is obtained. The total coating thickness is approximately 800 nanometers.

[0064] Working principle: The strongly hydrated layer formed by the PEG matrix effectively repels the initial adhesion of proteins and cells; the mesoporous silica nanoparticles possess excellent bioactivity, and their surface can adsorb and slowly release endogenous growth factors (VEGF, bFGF). Simultaneously, their degradation product, silicic acid, has a regulatory effect on fibroblasts, guiding them towards a more moderate phenotypic differentiation and promoting tissue repair rather than excessive fibrosis. Therefore, this embodiment achieves anti-adhesion by creating a microenvironment unfavorable to excessive fibroblast proliferation and guiding tissue towards benign healing.

[0065] This approach does not rely on exogenous drugs, avoiding potential toxic side effects and the complexities of regulatory approval. Its effects are closer to physiological regulation, with a higher expected long-term safety profile. It is particularly suitable for patients sensitive to drugs or those who wish to use non-pharmacological therapies.

[0066] Example 3:

[0067] This invention provides a surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery, comprising:

[0068] Substrate material layer 1: In this embodiment, expanded polytetrafluoroethylene (e-PTFE) membrane is also used, but its surface flatness is required to be high.

[0069] Surface functional coating 2: A coating with a specific nano-topological structure bonded to one side of the e-PTFE membrane.

[0070] Polymer matrix: Polycaprolactone (PCL) was selected. PCL has good spinnability and biodegradability, making it suitable for constructing fine topologies.

[0071] Nanofunctional components: In this embodiment, the “functional components” refer to the nanoscale topology of the coating itself, rather than added particles.

[0072] Coating Structure: The coating is a nonwoven fabric-like film formed by direct deposition of PCL nanofibers through electrospinning technology. The fiber diameter is between 300-500 nanometers, and the fibers form an intricate nanoscale network and porous structure. This is itself a specific "nanopockmarked / network" topology.

[0073] A method for preparing a surface nano-coating anti-adhesion material as described above includes the following steps:

[0074] Preparation of spinning solution: Dissolve PCL in a mixed solvent of dimethylformamide (DMF) and tetrahydrofuran (THF) to prepare a solution of a certain concentration.

[0075] Substrate fixation: The e-PTFE membrane is flatly fixed on the roller of the electrospinning receiving device.

[0076] Coating formation: Electrospinning is employed. Under specific voltage (e.g., 15kV), receiving distance (e.g., 15cm), and propulsion speed, PCL solution is sprayed onto the surface of the e-PTFE membrane. The PCL solution is stretched and cured in an electric field, forming ultrafine fibers that are randomly stacked to form a membrane.

[0077] Post-processing: The prepared material is vacuum dried to remove residual solvent.

[0078] Finished product: An e-PTFE membrane with a PCL nanofiber layer on its surface is obtained. The fiber layer is about 10 micrometers thick, but due to its porosity, its actual volume is small, and its impact on flexibility is negligible.

[0079] Working Principle: Cell behaviors (such as adhesion, spreading, and migration) are significantly influenced by the surface topology of the matrix on which they reside; this phenomenon is known as "contact guidance." Fibroblasts tend to adhere firmly and spread extensively on relatively flat, continuous surfaces, thereby secreting large amounts of collagen. However, the PCL nanofiber network constructed in this invention is a discontinuous, anisotropic, and complex topology. This topology is unfavorable for fibroblasts to form stable focal adhesions, thus inhibiting their full spreading and activation, ultimately leading to a decrease in their proliferation and collagen secretion capacity. In short, the surface nanotopology "deceives" the cells, making it difficult for them to adhere and function normally.

[0080] Suitable for clinical scenarios where the introduction of exogenous bioactive substances needs to be absolutely avoided, or as a long-lasting physical basis for other active coatings.

[0081] Example 4: Animal in vivo experiments to verify the anti-adhesion effect

[0082] This embodiment evaluates the in vivo anti-adhesion effect of the material of the present invention (taking the drug-loaded e-PTFE membrane described in Example 1 as an example) using a rat paraspinal muscle interspace implantation model.

[0083] Experimental materials and grouping:

[0084] Experimental group: The surface nano-coating anti-adhesion e-PTFE membrane prepared in Example 1 (coating side facing the muscle) was used.

[0085] Control group: Ordinary e-PTFE membrane of the same specifications without any coating treatment.

[0086] Experimental animals: 24 healthy adult SD rats were randomly divided into an experimental group and a control group, with 12 rats in each group.

[0087] Experimental methods (operational steps):

[0088] After anesthetizing the rats, a longitudinal incision was made about 0.5 cm away from the spine on the back, and the muscle tissue was bluntly dissected to create an implantation gap of about 1 cm x 1 cm between the lumbar fascia and the erector spinae muscle.

[0089] Insert the pre-cut experimental or control group material (approximately 0.8cm x 0.8cm) into the gap, ensuring the material is flat.

[0090] Suture the muscle fascia and skin incisions.

[0091] Routine feeding was performed post-surgery. Six rats from each group were sacrificed at two time points, week 4 and week 12 post-surgery, for observation.

[0092] The evaluation indicators and results are shown in the table below:

[0093] General observation of the degree of adhesion The adhesions are dense and extensive, making them difficult to separate blunt force, and separation is prone to bleeding. The adhesion is slight, the gaps are clearly visible, and it is easy to separate without damage. H&E staining (inflammation and cell proliferation) Extensive infiltration of inflammatory cells, significant proliferation of fibroblasts, and the material being tightly wrapped by a thick layer of granulation tissue. The inflammatory response is mild, and only a very thin tissue layer or gaps are visible on the material surface. Masson staining (collagen deposition) A large amount of dense blue collagen fibers are deposited, forming a strong fiber encapsulation layer. Collagen fiber deposition is significantly reduced, and the arrangement is loose. Percentage of collagen-positive area (35.7±4.1)% (5.2±1.8)% Adhesion score (0-4 points) 3.5±0.4 0.8±0.3 qPCR (gene expression) TGF-β1 and Col1a1 are highly expressed. TGF-β1 decreased to 70%, Col1a1 decreased to 65%, and IL-10 was slightly upregulated.

[0094] Gross observation: The implant and surrounding tissue were removed. In the control group, the material showed dense and extensive adhesions to the surrounding muscle tissue, making blunt dissection difficult and forcibly separating it easily leading to tissue bleeding. In the experimental group, the material showed significantly less adhesion to the surrounding tissue, with clear gaps visible in most cases, facilitating easy, non-traumatic separation.

[0095] Histological evaluation: The implant-tissue interface was paraffin-embedded, sectioned, and stained with hematoxylin and eosin (H&E) and Masson trichrome.

[0096] H&E staining: In the control group, extensive inflammatory cell infiltration and fibroblast proliferation were observed, with the material surface tightly wrapped by a thick layer of granulation tissue. In the experimental group, the inflammatory response was mild, with only a very thin tissue layer or gaps visible on the material surface.

[0097] Masson staining: In the control group, a large number of dense blue collagen fibers were deposited at the interface, forming a strong fiber encapsulation layer; in the experimental group, collagen fiber deposition was significantly reduced and the fibers were loosely arranged.

[0098] To further quantify collagen deposition, image analysis software was used to analyze the percentage of positive area in Masson stained sections. The results showed that at 12 weeks post-operation, the percentage of positive collagen area in the material-tissue interface region of the experimental group was only (5.2±1.8)%, while that of the control group was as high as (35.7±4.1)%, with a highly significant difference (P<0.001).

[0099] Adhesion severity scoring: The recognized adhesion scoring standard (0-4 points: 0 = no adhesion, 4 = dense adhesion) was used. At 12 weeks postoperatively, the mean adhesion score of the experimental group was significantly lower than that of the control group (mean score of experimental group 0.8±0.3 vs. mean score of control group 3.5±0.4, P<0.01).

[0100] Local tissue samples were collected for real-time quantitative PCR detection. Compared with the control group, the mRNA expression levels of key pro-fibrotic factors TGF-β1 and type I collagen (Col1a1) in the experimental group were significantly downregulated (reduced by approximately 70% and 65%, respectively), while the expression of the anti-inflammatory factor IL-10 was slightly upregulated. This molecular biological result confirms at the gene expression level that the coating material of this invention effectively regulates the molecular signaling pathway of local healing through sustained-release drug (dexamethasone), inhibits the fibrosis process, and provides microscopic mechanism support for the macroscopic anti-adhesion effect.

[0101] Experimental conclusion:

[0102] The results of this animal experiment demonstrate that, compared to uncoated ordinary e-PTFE membranes, the surface nano-coated anti-adhesion material provided by this invention significantly reduces tissue inflammation at the implantation site, effectively inhibits fibroblast proliferation and collagen fiber deposition, thereby achieving excellent anti-adhesion effects in vivo. This directly verifies that the technical concept of "inhibiting fibroblast adhesion through a dual mechanism of physical barrier and bioactivity regulation" described in this invention is successful and effective.

[0103] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. A surface nanocoating anti-adhesion material for sacral cyst encasement, characterized in that, include: A sheet-like base material layer is used to wrap the sacral canal cyst; And a surface functional coating bonded to at least one surface of the substrate material layer; The surface functional coating is a nano-coating, which is configured to inhibit fibroblast adhesion through a dual mechanism of physical barrier and bioactivity regulation; The surface functional coating is composed of a biocompatible polymer matrix and nano-functional components dispersed in the polymer matrix.

2. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 1, characterized in that, The base material layer is a stitchable artificial diaphragm or expanded polytetrafluoroethylene membrane.

3. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 1, characterized in that, The polymer matrix is ​​selected from one or more of polyethylene glycol and its derivatives, phospholipid polymers, and polylactic acid-glycolic acid copolymers.

4. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 1, characterized in that, The nanofunctional component is at least one of drug-loaded nanoparticles, bioactive nanoparticles, and surface topological structure nanounits.

5. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 4, characterized in that, The drug-loaded nanoparticles are loaded with anti-inflammatory or anti-fibrotic drugs, wherein the anti-inflammatory drug is dexamethasone or methylprednisolone; and the anti-fibrotic drug is mitomycin C or 5-fluorouracil.

6. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 4, characterized in that, The bioactive nanoparticles are selected from nano-hydroxyapatite or mesoporous silica nanoparticles.

7. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 4, characterized in that, The surface topology nanounits are arrays of nanopillars or nanopits formed on the coating surface.

8. The surface nano-coating anti-adhesion material for sacral canal cyst wrapping surgery according to claim 1, characterized in that, The thickness of the surface functional coating is 50 nanometers to 5 micrometers.

9. A method for preparing a surface nano-coating anti-adhesion material as described in any one of claims 1-8, characterized in that, Includes the following steps: A coating solution containing a polymer matrix and nano-functional components is prepared, and a surface functional coating is formed on the surface of a substrate material using dip-coating-coating, spraying, electrospinning, or layer-by-layer self-assembly methods. The material is then obtained after drying or cross-linking and curing.

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