A method for manufacturing a porous carbon scaffold for medical implants

Abstract

The application discloses a kind of manufacturing methods of porous carbon scaffold for medical implant, it is related to the technical field of biomedical materials, preparation steps are as follows: S1, precursor preparation, organic matter, foaming agent and auxiliary agent are mixed according to mass ratio 70-90:5-20:3-10, after mixing, nano-particle is added, high-speed shearing dispersion is carried out to nano-particle, and evenly dispersed in precursor;S2, solidification, by solidification crosslinking reaction to form the matrix with stable three-dimensional network structure, the open porosity of three-dimensional network structure is 60-95%, pore size distribution is 10-500 μm, magnetic field is introduced in solidification process.The porous carbon scaffold prepared in the application has excellent physical and biological properties: porosity reaches 60-90%, compression strength is greater than or equal to 10MPa, pore connectivity rate is greater than or equal to 90%, its high porosity and three-dimensional connected structure create conditions for uniform deposition of coating, can realize inside and outside surface synchronous coverage, solve the problem of uneven coating of traditional dense base material, the balance of lightweight and high mechanical strength of porous carbon is formed.

Description

Technical Field

[0001] This invention relates to the field of biomedical materials technology, specifically to a method for manufacturing a porous carbon scaffold for medical implants. Background Technology

[0002] With the accelerating aging of the global population and the rising incidence of traumatic and degenerative diseases, the clinical demand for medical implants such as artificial joints, heart valves, dental implants, and bone fixation devices is continuously increasing. As core medical devices for repairing the function of human tissues and organs, technological innovation in the manufacturing of medical implants directly affects clinical treatment outcomes and patients' quality of life. This field, as a core interdisciplinary area of ​​modern medicine and advanced manufacturing technology, has already developed extensive technological applications in areas such as medical repair, health monitoring, and biological function enhancement.

[0003] Traditional medical implant manufacturing primarily utilizes metal and ceramic substrates. Traditional metal or ceramic substrates, such as titanium alloys and alumina, are mostly dense structures, presenting the following problems: Traditional processes lack the capability to handle complex designs such as porous structures and gradient materials, resulting in low specific surface area. The limited usable surface area of ​​dense materials makes it difficult to achieve efficient loading and uniform distribution of functional coatings; poor permeability, as the closed structure hinders the flow of gas or liquid within the material, leading to coatings in processes like chemical vapor deposition (CVD) only covering the surface, leaving the interior untreated. This makes it difficult to optimize the biomechanical compatibility of the implant with human tissue and to impart bioactive functions that induce cell adhesion and blood vessel ingrowth; insufficient mechanical adaptability, as the excessive rigidity of dense materials, such as titanium alloys with an elastic modulus far exceeding that of human bone, easily triggers a "stress shielding effect," leading to bone resorption or loosening around the implant.

[0004] Porous implants, with their unique structural advantages, have seen rapid development in orthopedics, dentistry, and soft tissue repair in recent years, becoming a research hotspot in biomedical engineering. The porous structure of porous implants allows new bone tissue to grow into the pores, forming a mechanical interlock, improving the bonding strength between the implant and the host bone, and reducing the risk of loosening. Their porous structure not only mimics the microscopic morphology of natural bone tissue but also optimizes mechanical fit and promotes tissue regeneration by controlling porosity, pore size, and connectivity. Porous structures can also serve as carriers for loading antibiotics, achieving localized sustained release, reducing infection, and promoting bone regeneration. Therefore, we propose a method for manufacturing porous carbon scaffolds for medical implants. Summary of the Invention

[0005] To solve the above-mentioned technical problems, a method for manufacturing a porous carbon scaffold for medical implants is provided. This technical solution solves the above-mentioned problems.

[0006] To achieve the above objectives, the technical solution adopted by this invention is: a method for manufacturing a porous carbon scaffold for medical implants, comprising the following steps:

[0007] S1. Preparation of precursor: Organic matter, foaming agent and additives are mixed in a mass ratio of 70-90:5-20:3-10. After mixing, nanoparticles are added and the nanoparticles are dispersed by high-speed shearing to uniformly disperse in the precursor.

[0008] S2. Curing: A matrix with a stable three-dimensional network structure is formed through a curing crosslinking reaction. The porosity of the three-dimensional network structure is 60-95%, and the pore size distribution is 10-500μm. A magnetic field is introduced during the curing process to induce the magnetic and polar molecules in the precursor to oriented and regulate the anisotropy of the three-dimensional network structure.

[0009] S3. Carbonization treatment: The solidified matrix is ​​placed in an inert atmosphere furnace. The pre-carbonization stage ensures the initial stable carbonization of the matrix. Then, the graphitization degree of the carbon skeleton is improved by directional thermal gradient and mechanical stress loading to form a porous carbon skeleton.

[0010] S4. Purification treatment: Purification with chlorine or fluorine-containing gas and high-temperature calcination to remove impurities from the carbon skeleton, controlling the impurity content to ≤0.5wt%.

[0011] S5. Surface processing: The purified carbon support is cleaned and decontaminated, and the surface is roughened to a surface roughness Ra≤5μm.

[0012] Preferably, in step S1, the organic material is asphalt; the foaming agent is sodium bicarbonate; the additive is nano-silica dispersant; and the nanoparticles are one of elemental metal nanoparticles, alloy nanoparticles, and oxide nanoparticles.

[0013] Preferably, the high-speed shear dispersion step of the nanoparticles in step S1 is as follows:

[0014] Start the high-speed shear disperser to stir the nanoparticles. In the first stage, the speed is set to 8000-12000 r / min and the shearing time is 15-30 min to break up the nanoparticle agglomerates and reduce their particle size to the nanoscale.

[0015] Second stage: Increase the rotation speed to 15000-20000 r / min, and the shearing time to 10-20 min to further refine the particles and form a dispersion system;

[0016] The working status is monitored in real time during the shearing and dispersion process.

[0017] Preferably, in step S2, the curing temperature is increased to 280℃ at a rate of 5℃ / min and held for 4 hours; a magnetic field is introduced during the curing process to regulate the magnetic and polar molecules in the precursor, specifically as follows:

[0018] Prepare equipment to generate a uniform strong magnetic field, a temperature-controlled curing oven, and a non-magnetic mold, and inspect the precursor materials;

[0019] The precursor is poured into a mold and placed in the center of a magnetic field. The magnetic field is activated in advance and its intensity and direction are set while the product is in a liquid state.

[0020] During curing, maintain a stable magnetic field, control the heating rate, temperature, and time according to the process, and monitor structural changes with instruments.

[0021] After curing, the magnetic field was turned off, the sample was cooled and demolded, and performance tests were performed on the sample to evaluate the anisotropic effect.

[0022] Preferably, the steps for implementing the directional thermal gradient in step S3 are as follows:

[0023] Pre-carbonization stage: Hold at 300-600℃ for 0.5-2h, with a heating rate ≤3℃ / min;

[0024] High-temperature carbonization stage: hold at 800-1500℃ for 1-4 hours, with a heating rate of 5-10℃ / min, and the temperature uniformity deviation inside the furnace is ≤±10℃; the inert atmosphere is argon or nitrogen, and the oxygen content is <10ppm.

[0025] A multi-zone independent temperature control system is set up in the carbonization furnace, with a temperature difference of 50-200℃ between adjacent zones, and the gradient direction is parallel to the principal stress direction of the carbon skeleton.

[0026] Preferably, in step S4, the temperature is raised to 1200 to 1500 degrees Celsius, and a chlorine- or fluorine-containing gas is introduced for 45 to 60 hours; the high-temperature calcination treatment is carried out in an inert atmosphere at 1400 to 1600 degrees Celsius for 2 to 4 hours to volatilize metallic impurities Fe and Na.

[0027] Preferably, the specific steps in step S4 are as follows:

[0028] Heat to 1200 to 1500 degrees Celsius and introduce chlorine or fluorine-containing gas for 45-60 hours;

[0029] High-temperature calcination treatment is carried out at 1400-1600℃ in an inert atmosphere for 2-4 hours;

[0030] Preferably, the surface processing step in step S5 is as follows:

[0031] The carbon support is ultrasonically cleaned at a frequency of 40-80kHz for 10-30 minutes to remove adsorbed organic matter, dust and processing residues from the surface. Then, a surface roughening process is selected for roughening.

[0032] Preferably, the surface roughening treatment in step S5 is carried out by chemical vapor deposition. The carbon scaffold is placed in the CVD reaction chamber, and a carbon source gas is introduced. The carbon source gas is decomposed at high temperature to generate a thin layer of carbon nanotubes or graphene, which covers the surface to form rough protrusions.

[0033] Preferably, the prepared porous carbon scaffold has the following properties: porosity of 60-90%, compressive strength ≥10MPa; and pore connectivity of the carbon scaffold ≥90%.

[0034] Compared with the prior art, the beneficial effects of the present invention are as follows:

[0035] The mesh-like porous carbon scaffold prepared by this invention possesses excellent physical and biological properties: a porosity of 60-90%, a compressive strength ≥10MPa, and a pore connectivity ≥90%. Its high porosity and three-dimensional interconnected structure create conditions for uniform deposition of the coating, enabling simultaneous coverage of the inner and outer surfaces. This solves the problem of uneven coating in traditional dense substrates. The lightweight and high mechanical strength of porous carbon form a balance, providing stable support for the coating and ensuring the mechanical fit of the implant, thus providing an innovative solution for the efficient preparation of medical implants. Attached Figure Description

[0036] Figure 1 This is a flowchart illustrating the manufacturing steps of the porous carbon scaffold of the present invention. Detailed Implementation

[0037] The following description is intended to disclose the invention and enable those skilled in the art to implement it. The preferred embodiments described below are merely examples, and other obvious variations will occur to those skilled in the art.

[0038] Example 1

[0039] A method for manufacturing a porous carbon scaffold for medical implants, comprising the following specific preparation steps:

[0040] First, a precursor is prepared by mixing organic matter (asphalt), foaming agent (sodium bicarbonate), and additive (nano silica dispersant) in a mass ratio of (70-90):(5-20):(3-10). Asphalt with a high softening point and low impurities is preferred to ensure the formation of a stable carbon skeleton after carbonization. After mixing, nanoparticles are added and subjected to high-speed shear dispersion to uniformly disperse them in the precursor. The nanoparticles are stirred by starting a high-speed shear disperser. In the first stage, the rotation speed is set to 8000-12000 r / min and the shearing time is 15-30 min to break up the nanoparticle agglomerates and reduce their particle size to the nanoscale. In the second stage, the rotation speed is increased to 15000-20000 r / min and the shearing time is 10-20 min to further refine the particles and form a dispersed precursor system.

[0041] Nanoparticles possess extremely large specific surface areas and high surface energy, making them highly prone to aggregation, forming micron-sized aggregates. The first stage of low-speed shearing (8000-12000 r / min) provides sufficient shear force to break up these large aggregates, successfully reducing the particle size of nanoparticles to the nanoscale. This initial low-speed shearing lays the foundation for subsequent high-speed refining, ensuring the stability of the entire dispersion process. The second stage of high-speed shearing (15000-20000 r / min) further reduces the particle size, and with the help of strong turbulence, the nanoparticles achieve a more uniform distribution in the asphalt matrix. This increases the interfacial area between nanoparticles and asphalt, enhances the interfacial bonding force, and significantly improves the overall performance of the composite material.

[0042] The curing process causes asphalt molecules to form a three-dimensional network structure, preventing the structure from collapsing due to high-temperature melting during subsequent carbonization. It also avoids excessive shrinkage or pore blockage of the porous structure. The mixture is injected into a molding die and placed in a constant temperature chamber for curing and cross-linking. It is kept at 150-280℃ for 2-4 hours to promote the formation of a covalent bond network between asphalt molecules, triggering the decomposition of the foaming agent and releasing gases such as CO2, thus forming a matrix with a stable three-dimensional network structure.

[0043] A magnetic field is introduced during the curing process to regulate the magnetic and polar molecules in the precursor. The magnetic field can induce the magnetic and polar molecules in the precursor to oriented and arrange themselves in anisotropy, so that the three-dimensional network structure exhibits anisotropy, such as forming ordered pores or fiber orientation in a specific direction, to meet the directional requirements of different applications for material properties (such as directional enhancement of mechanical strength and conductivity).

[0044] By combining the design of porosity (60-95%) and pore size distribution (10-500μm), anisotropic structures can further regulate pore connectivity and spatial distribution, making them suitable for biomedical fields (such as directed cell growth and tissue engineering scaffolds) or energy storage (such as electrolyte transport path optimization).

[0045] The carbonization process is carried out in a pure inert atmosphere to avoid material oxidation or structural damage. The carbonization is carried out in two stages: the pre-carbonization stage is held at 300-600℃ for 0.5-2h with a heating rate ≤3℃ / min to ensure the initial stability of the matrix; the high-temperature carbonization stage is heated to 800-1500℃ at a rate of 5-10℃ / min and held for 1-3h, with a temperature uniformity deviation of ≤±10℃ in the furnace to avoid local overheating or undercooling that could lead to structural defects. To improve the graphitization degree of the carbon skeleton, a directional thermal gradient can be used during or after carbonization to make the carbon interlayer spacing ≤0.35nm, thereby optimizing the material's order and mechanical properties.

[0046] In the purification process, impurities are removed by purifying with chlorine or fluorine-containing gases and then calcining at high temperatures to ensure that the impurity content is ≤0.5wt%. Specifically, the process involves heating to 1200 to 1500 degrees Celsius and purifying with chlorine or fluorine-containing gases for 45-60 hours; followed by high-temperature calcination at 1400-1600 degrees Celsius in an inert atmosphere for 2-4 hours to volatilize metallic impurities Fe and Na.

[0047] Porous carbon scaffolds used in medical implants require surface treatment. The surface processing steps include ultrasonic cleaning (frequency 40-80kHz, time 10-30min) to thoroughly remove organic matter, dust and residues from the surface. Subsequently, surface roughening treatment is performed according to coating requirements to control the surface roughness Ra≤5μm, providing an ideal substrate for subsequent coating processes.

[0048] The mesh-like porous carbon scaffold prepared by the above process possesses excellent physical and biological properties: a porosity of 60-90%, compressive strength ≥10MPa, and pore connectivity ≥90%. Its high porosity and three-dimensional interconnected structure create conditions for uniform coating deposition, enabling simultaneous coverage of both inner and outer surfaces, thus solving the problem of uneven coatings on traditional dense substrates. Simultaneously, the lightweight and high mechanical strength of porous carbon achieve a balance, providing stable support for the coating and ensuring the mechanical fit of the implant, offering an innovative solution for the efficient fabrication of medical implants.

[0049] Comparative Example 1

[0050] The manufacturing steps for carbon scaffolds used in medical implants are as follows:

[0051] Biocompatible polymers were selected as the matrix, and carbon fiber types were chosen according to mechanical requirements. Surface modification and dispersion treatments were performed on the carbon fibers to enhance the interfacial bonding force with the matrix and prevent agglomeration.

[0052] The polymer is heated and melted, carbon fibers are added in proportion, and the mixture is uniformly mixed through an extruder to form a composite material.

[0053] After the composite material is filament-made, it is stacked layer by layer to form a shape. The prepreg is placed in a mold and pressed to form a nanofiber scaffold under a high voltage electric field.

[0054] Improving biocompatibility through chemical and physical methods;

[0055] Depending on the material properties, ethylene oxide, gamma ray, or high-pressure steam sterilization can be selected to ensure sterility and complete the preparation.

[0056] Performance testing of Example 1 and Comparative Example 1

[0057] Microstructure observation

[0058] Sample preparation: The two types of carbon support structures were cut into 5mm×5mm×2mm pieces using a cutting machine. The sample surfaces were then sanded with metallographic sandpaper from coarse to fine (100-2000 grit) in sequence. Polishing compound was then applied to the samples on a polishing machine to make the surfaces smooth and flat. The prepared samples were then fixed onto the SEM sample stage using conductive adhesive.

[0059] Observation and photography: Place the sample stage in a scanning electron microscope. First, observe the overall morphology of the sample at a low magnification (500x). After determining the region of interest, gradually increase the magnification (2000x, 5000x, 10000x) and take microscopic structure photos at different magnifications to record fiber distribution, pore morphology and other characteristics.

[0060] Relevant parameter settings: accelerating voltage 15kV, working distance 10mm, scanning mode is secondary electron imaging.

[0061] Mechanical property testing

[0062] Sample preparation: According to the fixture requirements of the universal testing machine, the two types of carbon supports were cut into strip-shaped specimens with dimensions of 50mm×10mm×2mm. Five parallel specimens were prepared for each group of samples.

[0063] Test procedure: The specimen is mounted on the fixture of the universal testing machine. The tensile speed is set to 2 mm / min. The tensile test is carried out, and the maximum load when the specimen breaks is recorded. The tensile strength is calculated according to the formula: tensile strength = maximum load / specimen cross-sectional area. In the compression test, the compression speed is set to 1 mm / min. The stress-strain curve during the compression process is recorded, and the compressive strength and elastic modulus are calculated.

[0064] Biocompatibility testing

[0065] Cell culture: In a biosafety cabinet, fibroblasts were seeded into culture dishes containing cell culture medium and placed in a carbon dioxide incubator (temperature 37℃, humidity 95%, CO2 concentration 5%) for 24 hours to allow the cells to adhere and grow.

[0066] Sample processing and cell seeding: Both types of carbon scaffolds were sterilized by immersion in 75% ethanol for 30 min, then rinsed three times with sterile PBS buffer for 5 min each time. The treated carbon scaffolds were then placed into 24-well cell culture plates, and each well was seeded with an appropriate amount of cell suspension (cell density 1×10⁶). 5 (number / mL), continue culturing in a carbon dioxide incubator;

[0067] Cell viability assay: Cell viability was assessed using a CCK-8 assay kit after 1, 3, and 7 days of culture.

[0068] The specific procedure is as follows: add 10 μL of CCK-8 reagent to each well, continue culturing for 2 hours, measure the absorbance value at a wavelength of 450 nm using an ELISA reader, and calculate the cell viability based on the standard curve.

[0069] Cell morphology observation: After 7 days of culture, the culture medium was discarded, and the cells were washed twice with PBS buffer for 5 min each time; then the cells were fixed with 4% paraformaldehyde for 30 min, the fixative was discarded, and the cells were washed three times with PBS buffer for 5 min each time.

[0070] Cells were stained with cell staining reagents (such as Hoechst 33342 and phalloidin) and their morphology and distribution were observed under an inverted microscope.

[0071] Pore ​​feature analysis

[0072] Sample preparation: Take appropriate amounts of each of the two types of carbon support, crush them into smaller particles, and put them into the sample tube of the pore size analyzer, ensuring that the sample is filled evenly and does not exceed two-thirds of the sample tube volume.

[0073] Test procedure: The sample tube is installed on the pore size analyzer and degassed. Vacuum degassing is performed at 120℃ for 4 hours to remove the gas adsorbed on the sample surface.

[0074] Using helium as the carrier gas and liquid nitrogen as the coolant, nitrogen adsorption-desorption experiments were conducted. The adsorption pressure range was set from 0.001 to 0.99P / P0 (P is the adsorption pressure and P0 is the saturated vapor pressure). The amount of nitrogen adsorbed and desorbed at different pressures was recorded. Based on the adsorption-desorption isotherm, the specific surface area was calculated using the BET method, and the pore size distribution and pore volume were calculated using the BJH method.

[0075] Data Recording and Analysis

[0076] Record microstructure photographs, mechanical property test data (tensile strength, compressive strength, elastic modulus), biocompatibility test data (cell viability, cell morphology description), and pore characteristic analysis data (specific surface area, pore size distribution, pore volume).

[0077] Statistical analysis was performed on the two sets of data. The t-test was used to compare the differences in various performance parameters of the carbon scaffolds in the comparative and example cases to determine whether the differences were statistically significant (P<0.05 indicates significant difference).

[0078] The foregoing has shown and described the basic principles, main features, and advantages of the present invention. Those skilled in the art should understand that the present invention is not limited to the above embodiments. The embodiments and descriptions in the specification are merely principles of the invention. Various changes and modifications can be made to the invention without departing from its spirit and scope, and all such changes and modifications fall within the scope of the claimed invention.

Claims

1. A method for manufacturing a porous carbon scaffold for a medical implant, characterized in that, The preparation steps are: S1, precursor preparation, mixing organic matter, foaming agent and additive according to mass ratio 70-90:5-20:3-10, after mixing, adding nanoparticles, high-speed shearing dispersion is carried out on the nanoparticles, and the nanoparticles are uniformly dispersed in the precursor; the additive is nano-silicon dioxide dispersant; the nanoparticles are one of metal element nanoparticles, alloy nanoparticles and oxide nanoparticles; S2, curing, forming a matrix with a stable three-dimensional network structure through curing cross-linking reaction, the three-dimensional network structure has an open porosity of 60-95%, and a pore size distribution of 10-500 μm, a magnetic field is introduced during the curing process, and the magnetic and polar molecules in the precursor are induced to directional arrangement, and the anisotropy of the three-dimensional network structure is controlled; S3, carbonization treatment, placing the matrix obtained after curing in an inert atmosphere furnace, ensuring the preliminary stable carbonization of the matrix in the pre-carbonization stage, and avoiding local overheating or supercooling to cause structural defects in the high-temperature carbonization stage; in the carbonization process, the graphitization degree of the carbon skeleton is improved through directional thermal gradient and mechanical stress loading, and a porous carbon skeleton is formed; S4, purification treatment, using chlorine-containing or fluorine-containing gas purification method to remove impurities in the carbon skeleton with high-temperature calcination method, and controlling the impurity content to be ≤0.5wt%; S5, surface processing, surface cleaning and decontamination treatment, and surface roughening are carried out on the purified carbon scaffold, and the surface roughness Ra is ≤5 μm.

2. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, In S1 step, the organic matter is pitch; the foaming agent is sodium bicarbonate.

3. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, In S1 step, the high-speed shearing dispersion step for the nanoparticles is: Starting the high-speed shearing dispersion machine, stirring the nanoparticles, setting the first stage speed to 8000-12000 r / min, and shearing for 15-30 min to break the nanoparticle agglomerates and reduce the particle size to nanoscale; The second stage speed is increased to 15000-20000 r / min, and the shearing time is 10-20 min to further refine the particles and form a dispersion system; The working state is monitored in real time during the shearing dispersion process.

4. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, In S2 step, the curing temperature is increased to 280℃ at a rate of 5℃ / min, and the temperature is kept for 4h; during the curing process, the magnetic and polar molecules in the precursor are controlled by introducing a magnetic field, and the specific steps are as follows: Prepare the equipment for generating a uniform strong magnetic field, the temperature-controlled curing furnace and the non-magnetic mold, and check the precursor material; Pour the precursor into the mold and place it in the center of the magnetic field, and start the magnetic field in advance when it is in a liquid state and set the intensity and direction; Keep the magnetic field stable during curing, control the heating rate, temperature and time according to the process, and monitor the structure change with the instrument; After curing, turn off the magnetic field, cool and demold, and test the performance of the sample to evaluate the anisotropy effect.

5. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, In S3 step, the implementation steps of directional thermal gradient are as follows: Pre-carbonization stage: keeping the temperature at 300-600℃ for 0.5-2h, and the heating rate is ≤3℃ / min; High-temperature carbonization stage: keeping the temperature at 800-1500℃ for 1-4h, and the heating rate is 5-10℃ / min, and the temperature uniformity deviation in the furnace is ≤±10℃; the inert atmosphere is argon or nitrogen, and the oxygen content is <10 ppm; A multi-zone independent temperature control system is arranged in the carbonization furnace, and the temperature difference between adjacent temperature zones is 50-200 DEG C, and the gradient direction is parallel to the main stress direction of the carbon skeleton.

6. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, The purification method of the chlorine-containing or fluorine-containing gas in the S4 step is heating to 1200-1500 DEG C, and the chlorine-containing or fluorine-containing gas is introduced for 45-60 hours; the high-temperature calcination method is to volatilize the metal impurities Fe and Na in an inert atmosphere at 1400-1600 DEG C for 2-4 hours.

7. The method of claim 1, wherein the porous carbon scaffold for a medical implant is produced by the steps of: The surface processing step in the S5 step is: The carbon support is subjected to ultrasonic cleaning, the frequency is 40-80 kHz, and the time is 10-30 min, so that the organic matter, dust and processing residues adsorbed on the surface are removed, and a surface roughening process is selected to perform roughening processing.

8. The method of claim 1, wherein the porous carbon scaffold for a medical implant is characterized by, The surface roughening treatment in the S5 step is treated by a chemical vapor deposition method, the carbon support is placed in a CVD reaction chamber, carbon source gas is introduced, and carbon nanotubes or graphene thin layers are generated by decomposition at high temperature to cover the surface to form rough protrusions.

9. The method of claim 1, wherein the porous carbon scaffold for a medical implant is produced by, The prepared porous carbon support has the following performances: porosity is 60-90%, compression strength is greater than or equal to 10 MPa; and the pore connectivity rate of the carbon support is greater than or equal to 90%. The prepared porous carbon support has the following performances: porosity is 60-90%, compression strength is greater than or equal to 10 MPa; and the pore connectivity rate of the carbon support is greater than or equal to 90%.

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