WO2018196055A1 - 高分子材料表面改性方法及其产品和用途 - Google Patents

高分子材料表面改性方法及其产品和用途 Download PDF

Info

Publication number
WO2018196055A1
WO2018196055A1 PCT/CN2017/084811 CN2017084811W WO2018196055A1 WO 2018196055 A1 WO2018196055 A1 WO 2018196055A1 CN 2017084811 W CN2017084811 W CN 2017084811W WO 2018196055 A1 WO2018196055 A1 WO 2018196055A1
Authority
WO
WIPO (PCT)
Prior art keywords
polymer material
ion implantation
plasma immersion
immersion ion
biomolecule
Prior art date
Application number
PCT/CN2017/084811
Other languages
English (en)
French (fr)
Inventor
王怀雨
高昂
朱剑豪
Original Assignee
深圳先进技术研究院
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 深圳先进技术研究院 filed Critical 深圳先进技术研究院
Publication of WO2018196055A1 publication Critical patent/WO2018196055A1/zh

Links

Images

Classifications

    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J7/00—Chemical treatment or coating of shaped articles made of macromolecular substances
    • C08J7/12—Chemical modification
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J2327/00—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by a halogen; Derivatives of such polymers
    • C08J2327/02—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by a halogen; Derivatives of such polymers not modified by chemical after-treatment
    • C08J2327/12—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by a halogen; Derivatives of such polymers not modified by chemical after-treatment containing fluorine atoms
    • C08J2327/18—Homopolymers or copolymers of tetrafluoroethylene
    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
    • C08J2361/00—Characterised by the use of condensation polymers of aldehydes or ketones; Derivatives of such polymers
    • C08J2361/04—Condensation polymers of aldehydes or ketones with phenols only
    • C08J2361/16—Condensation polymers of aldehydes or ketones with phenols only of ketones with phenols

Definitions

  • the invention relates to a surface modification method of a polymer material, and a product and a use thereof, the surface modification method particularly relates to a surface of a medical polymer material treated by plasma immersion ion implantation and a covalently grafted organism on the surface after treatment Active molecules to achieve their biochemical modification.
  • Polymer materials also known as polymer materials, are widely used in the biomedical field for the repair, replacement and regeneration of living tissues, as well as for care and medical appliances. Due to its special application environment (need to directly contact with human body fluids, blood, organs, tissues, etc.), biomedical polymer materials must have good physical and mechanical properties, chemical stability, non-toxicity, and easy processing and formability. It must also have biocompatibility, medical functionality, and the like. Since the biological properties of medical polymer materials are mainly determined by the physicochemical properties of their surfaces, surface modification can improve their biological properties or give them some special biology without affecting their own advantages. Features.
  • biomimetic modification of medical polymer materials that is, biologically active macromolecules such as proteins, polysaccharides, polypeptides, cell growth factors, etc.
  • the surface forms a stable bio-transition layer that interacts specifically with the biological environment to further enhance the biological properties of the material or confer specific biological functions.
  • the grafting of heparin and hirudin on the surface of artificial blood vessels constructed of polytetrafluoroethylene can achieve the effect of inhibiting thrombus formation, thereby greatly improving the long-term patency rate of artificial blood vessels (Hoshi R A, Van Lith R, Jen M C, Et al.
  • wet chemical crosslinking techniques is not only relatively complicated and cumbersome, but also introduces toxic organic crosslinking reagents. More importantly, this chemical method is difficult to graft a variety of bioactive molecules on the surface at the same time, and the sequential grafting of multiple biomolecules makes the grafting process extremely cumbersome and difficult to achieve.
  • the object of the present invention is to provide a simple and feasible method for surface modification biochemical modification of a polymer material, and a product and use thereof, the surface modification method particularly relates to a medical treatment based on gas plasma immersion ion implantation (ie, gas PIII)
  • gas PIII gas plasma immersion ion implantation
  • the bioactive molecule is covalently grafted onto the surface of the molecular material and on the treated surface to effect its biochemical modification.
  • the modification method provided by the invention does not need to use a chemical crosslinking agent, firstly performs surface modification and activation of the medical biopolymer material by gas plasma immersion ion implantation, and then immerses the modified medical polymer material in containing biomolecules. After incubation for a period of time, the biologically active macromolecules can be covalently grafted onto the surface of the polymer material to achieve biochemical surface modification.
  • the grafting principle of the biomolecule on the surface of the medical material in the present invention is: in the process of modifying the polymer material by using the gas plasma immersion ion implantation technique, the collision of the injected high energy ions with the polymer chain and the charge and energy The transfer produces a large number of long-acting and highly active free radicals (Free Radical) on the surface of the polymer material.
  • Free Radical free radicals formed by high-energy ion bombardment can be preserved for a long time in the affected area of ion implantation and continuously migrate to the surface of the substrate.
  • the free radicals that reach the surface react with the molecules present in the environment and ultimately covalently graft the molecules onto the surface of the material.
  • the surface modification technical scheme adopted by the present invention can be divided into two steps: 1. gas plasma immersion ion implantation treatment; 2. incubation in a solution containing biomolecules.
  • a negative bias is applied to the sample disk used to accelerate the positively charged ions in the plasma and eventually inject them into the surface of the material.
  • the process parameters used for gas plasma immersion ion implantation include: background vacuum of 5 ⁇ 10 -4 to 9 ⁇ 10 -3 Pa, gas introduction flow rate of 10 to 200 sccm, and negative bias voltage of the sample tray of 5 to 50 kV.
  • the injection pulse width is 10 to 300 microseconds
  • the injection pulse frequency is 50 to 2000 Hz
  • the radio frequency power is 100 to 3000 W
  • the injection time is 30 to 300 minutes.
  • the preferred parameters are: the background vacuum is 1 ⁇ 10 -3 to 9 ⁇ 10 -3 Pa, the gas introduction flow rate is 20-100 sccm, the negative bias voltage of the sample tray is 10-30 kV, and the injection pulse width is 20-200.
  • the microsecond has an injection pulse frequency of 50 to 500 Hz, a radio frequency power of 100 to 1000 W, and an injection time of 30 to 180 minutes.
  • the most preferred parameters are: background vacuum of 5 ⁇ 10 -3 Pa, gas introduction flow rate of 30 sccm, sample tray with a negative bias of 15 kV, injection pulse width of 20 ⁇ sec, injection pulse frequency of 500 Hz, RF power It is 1000W and the injection time is 60-180 minutes.
  • the gas used in the gas plasma immersion ion implantation is not particularly required, and it is preferred to use a non-toxic gas for the needs of the field of application of the present invention.
  • Different gases may affect the density of surface free radicals after material modification, which affects the efficiency of grafting.
  • common gases such as oxygen, nitrogen, argon, ammonia, and hydrogen are used. Feasible of the invention Sex.
  • this method can be applied to all polymer materials that can withstand gas PIII technology, such as polyethylene, polytetrafluoroethylene, polystyrene, polyvinyl chloride, polypropylene, polyamide, polyetheretherketone (abbreviation). PEEK), polylactic acid, polyglycolic acid, polyurethane, poly(lactic-co-glycolic acid) copolymer, polybutylene succinate, polycaprolactone, polymethyl methacrylate, epoxy resin, polychlorinated Ethylene and the like.
  • gas PIII technology such as polyethylene, polytetrafluoroethylene, polystyrene, polyvinyl chloride, polypropylene, polyamide, polyetheretherketone (abbreviation). PEEK), polylactic acid, polyglycolic acid, polyurethane, poly(lactic-co-glycolic acid) copolymer, polybutylene succinate, polycaprolactone, polymethyl methacrylate, epoxy resin, polych
  • polyetheretherketone As an FDA-approved medical implant material, polyetheretherketone is not only light, bio-stable and non-biotoxic, but more importantly its elastic modulus (5-8GPa) than metal orthopedic implant materials. Closer to the human bones, and after being implanted in the body, X-ray transmission, MRI and computed tomography do not produce artifacts and many other biomedical advantages. However, PEEK is an inert biological material, and the lack of biocompatibility causes its Osseointegration to be insufficient after implantation and requires secondary surgery for correction.
  • polytetrafluoroethylene has excellent chemical stability, and thus it is difficult to carry out surface modification by chemical methods alone.
  • the polymer material in the present invention is preferably polytetrafluoroethylene or polyetheretherketone.
  • the polymer material treated by the gas plasma immersion ion implantation is incubated in a solution containing biomolecules.
  • the solution containing biomolecules is a buffer system capable of keeping biomolecules active, such as phosphate buffered saline (PBS) or physiological saline.
  • PBS phosphate buffered saline
  • physiological saline a buffer system capable of keeping biomolecules active, such as phosphate buffered saline (PBS) or physiological saline.
  • the temperature and time of incubation in a solution containing biomolecules is such that biomolecules remain biologically active during incubation.
  • the temperature of the incubation is usually selected at 4-37 ° C; the incubation time ensures that the grafting is completed; preferred conditions are, for example, incubation in a solution containing biomolecules at 4 ° C for more than 12 hours.
  • the loading of the biomolecule on the surface of the polymer material can be adjusted by the concentration of the biological solution used at the time of incubation, and the concentration of the biological solution is, for example, 10 to 2000 ⁇ g/mL, preferably 50 to 500 ⁇ g/mL.
  • Simultaneous loading of two or more biomolecules can be achieved by incubating for a period of time in a co-mixed solution of the corresponding biomolecule.
  • biomolecules can be carried out according to this, or the grafting can be carried out one or more times by separating the different parts and incubating with the corresponding different biomolecule solutions.
  • Grafting of different biomolecules can achieve different functions, such as polysaccharides (such as heparin), peptides (such as hirudin), proteins (such as horseradish peroxidase, transmembrane glycoprotein CD47), and cytokines. (such as human stromal cell-derived factor 1 ⁇ (SDF-1 ⁇ )) and the like.
  • polysaccharides such as heparin
  • peptides such as hirudin
  • proteins such as horseradish peroxidase, transmembrane glycoprotein CD47
  • cytokines such as human stromal cell-derived factor 1 ⁇ (SDF-1 ⁇ )
  • the surface of the polymer material immersed in the gas plasma immersion ion implantation is long-term effective in the ability to covalently load biomolecules by incubation in a solution containing biomolecules while being stored in the air.
  • the surface obtained by the method of the present invention is a biomolecule modified polymer material having a structure in which a surface layer of a polymer material has active radicals introduced by gas plasma immersion ion implantation, which react with biomolecules and Covalently grafted onto the surface of the material.
  • the present invention uses a gas plasma immersion ion implantation technique to treat a biomedical polymer material, and can covalently graft a bioactive macromolecule onto a surface of the material without using a chemical crosslinking agent. To achieve its biochemical surface modification.
  • the present invention has the following advantages:
  • Plasma immersion ion implantation technology eliminates the "line of sight limitation" of conventional beam line ion implantation.
  • the injection process is omnidirectional, and even surface samples with uniform morphology can be uniformly surface treated.
  • Plasma immersion ion implantation treatment can greatly improve the surface physicochemical properties, such as surface roughness, surface energy and surface chemical composition, without affecting the performance of polymer matrix. And using different gases for injection treatment, different surface physicochemical properties can be obtained.
  • the surface of the polymer material does not need to be treated with a chemical crosslinking agent, and only needs to be immersed in a solution containing biomolecules for a period of time to covalently load the bioactive molecules in the solution.
  • the surface modification method not only has simple and convenient operation, but also avoids the use of toxic chemical cross-linking agent, and is favorable for large-scale and industrial production.
  • the loading of biomolecules on the surface of the polymer material can be adjusted by the concentration of the solution used for incubation. And when a co-mixed solution of a plurality of biomolecules is used, a corresponding plurality of biomolecules can be covalently grafted to the surface of the polymer material after the plasma immersion ion implantation treatment.
  • Gas plasma immersion ion implantation Surface modified polymer material has no special requirements on the storage conditions after treatment. Even if stored in the air for a long time, its ability to covalently graft biomolecules by incubation in a solution containing biomolecules does not decrease significantly.
  • the biomimetic modification method for biomedical polymer materials provided by the invention has wide application prospects in the fields of medical implant materials, functional materials, bioactive materials, etc., and has simple process, low cost, and is suitable for batch and industrial production. .
  • Figure 1a is a scanning electron micrograph of the surface of a polytetrafluoroethylene that has not been subjected to plasma immersion ion implantation in Example 1.
  • Figure 1b is a scanning electron micrograph of the surface of a polytetrafluoroethylene treated by nitrogen plasma immersion ion implantation in Example 1.
  • Figure 1c is a scanning electron micrograph of the surface of a polytetrafluoroethylene treated by ammonia gas plasma immersion ion implantation in Example 1.
  • Fig. 1d is a scanning electron micrograph of the surface of polytetrafluoroethylene treated by nitrogen gas plasma immersion ion implantation in Example 1.
  • Example 2a is a three-dimensional picture, a cross-sectional profile, and its corresponding root mean square roughness (RMS) of an atomic force microscope of the surface of a polytetrafluoroethylene that has not been subjected to plasma immersion ion implantation in Example 2.
  • RMS root mean square roughness
  • 2b is a three-dimensional picture, a cross-sectional profile, and its corresponding root mean square roughness (RMS) of the surface of a polytetrafluoroethylene treated by nitrogen plasma immersion ion implantation in Example 2.
  • RMS root mean square roughness
  • 2c is a three-dimensional picture, cross-sectional profile, and its corresponding root mean square roughness (RMS) of the surface of the polytetrafluoroethylene treated by ammonia gas plasma immersion ion implantation in Example 2.
  • RMS root mean square roughness
  • 2d is a three-dimensional picture, a cross-sectional profile, and its corresponding root mean square roughness (RMS) of an atomic force microscope of the surface of a polytetrafluoroethylene treated by nitrogen gas plasma immersion ion implantation in Example 2.
  • RMS root mean square roughness
  • FIG. 3 is a full spectrum of X-ray photoelectron spectroscopy of the surface of a polytetrafluoroethylene material before and after gas plasma immersion ion implantation in Example 3.
  • FIG. 3 is a full spectrum of X-ray photoelectron spectroscopy of the surface of a polytetrafluoroethylene material before and after gas plasma immersion ion implantation in Example 3.
  • Example 4 is a graph showing the static contact angle of the surface of the polytetrafluoroethylene material before and after the gas plasma immersion ion implantation treatment in Example 4.
  • Fig. 5 is a graph showing the heparin loading density of the surface of the sample before and after the gas plasma immersion ion implantation treatment in Example 5 after incubation in a heparin solution.
  • Example 6 is a surface heparin loading density after the sample which has been subjected to gas plasma immersion ion implantation in Example 6 after being stored in the air for a corresponding period of time and then incubated in the heparin solution.
  • Figure 7 is a graph showing the long-term stability of heparin in the surface of polytetrafluoroethylene treated with nitrogen plasma immersion ion implantation in Example 7.
  • Figure 8 is a surface of Example 8 after plasma ion immersion ion implantation treatment and untreated surface after elution with phosphate buffer or 2% sodium dodecyl sulfate after loading horseradish peroxidase Retention of horseradish peroxidase.
  • Example 9 is a surface of the sample treated by each gas plasma immersion ion implantation in Example 9 after being stored in the air for a corresponding period of time and then loaded with horseradish peroxidase and eluted by 2% sodium dodecyl sulfate. Retention of horseradish peroxidase.
  • Figure 10 is a table of oxygen plasma immersion ion implantation treatment and non-treatment (PEEK control) in Example 10.
  • a sheet of polytetrafluoroethylene having a diameter of 15 mm and a thickness of 0.1 mm was sequentially ultrasonically cleaned with acetone, alcohol, and deionized water. This pretreated sample is called PTFE control.
  • the pretreated polytetrafluoroethylene is treated by a gas plasma immersion ion implantation technique.
  • the treatment is carried out by a method of injecting ammonia gas by nitrogen injection, ammonia injection, or nitrogen injection.
  • the specific treatment process is as follows: the background vacuum is 5 ⁇ 10 -3 Pa, the gas introduction flow rate is 30 sccm, the sample disk is loaded with a negative bias voltage of 15 kV, the injection pulse width is 20 microseconds, the injection pulse frequency is 500 Hz, and the RF power is It is 1000W.
  • the injection time of nitrogen gas is 180 minutes, the sample after the treatment is called N2PIII; the injection time of ammonia gas is 60 minutes, the sample after the treatment is called NH3PIII; after the injection of nitrogen for 180 minutes, the injection of ammonia gas is injected for 60 minutes.
  • This treated sample is referred to as N2+NH3PIII. (the same below)
  • the surface of the polytetrafluoroethylene before and after the gas plasma immersion ion implantation treatment was observed by a scanning electron microscope to obtain a photograph of the surface topography shown in FIG. It can be seen from Fig. 1 that the gas plasma immersion ion implantation treatment changes the surface morphology of the polytetrafluoroethylene to varying degrees.
  • the untreated PTFE control surface shown in Figure 1a is substantially flat, while the surface of the N2PIII sample after the nitrogen plasma injection shown in Figure 1b exhibits a quasi-regular nanoscale "valley"-like structure.
  • FIG. 1c is similar to the PTFE control surface, and the surface of the N2+NH3PIII sample after the nitrogen injection shown in Fig. 1d is similar to the surface of the N2PIII.
  • the ammonia gas plasma injection did not change the surface morphology of the polytetrafluoroethylene.
  • the surface roughness of the polytetrafluoroethylene sample obtained in the treatment of Example 1 was characterized by atomic force microscopy to obtain the three-dimensional picture, profile profile and corresponding mean square roughness (RMS) results of the surface shown in FIG. It can be seen from the three-dimensional picture of the surface in Fig. 2 that the results obtained by the atomic force microscope are substantially the same as those obtained by the scanning electron microscope in Example 1.
  • the surface roughness of the PTFE control shown in Figure 2a is 17.9 nm. Nitrogen plasma implantation significantly increased the surface roughness of the sample to 134 nm (Fig. 2b). The ammonia gas plasma injection had no effect on the surface roughness, and the mean square roughness after the treatment was 18.2 nm (Fig. 2c).
  • the surface mean square roughness of the ammonia gas injection after the nitrogen plasma injection was substantially the same as that of the nitrogen gas alone, and was 130 nm (Fig. 2d).
  • X-ray photoelectron spectroscopy wide field scanning was performed on the surface of the polytetrafluoroethylene sample obtained in Example 1, and the XPS full spectrum spectrum shown in Fig. 3 was obtained.
  • the abscissa indicates the binding energy and the ordinate indicates the peak intensity.
  • the nitrogen plasma immersion ion implantation site is known.
  • the fluorine content on the surface of the PTFE is reduced, and oxygen is introduced on the surface of the material; and the ammonia plasma immersion ion implantation treatment significantly reduces the surface fluorine content and significantly increases the surface nitrogen element. And the proportion of oxygen.
  • the surface wettability of the material was tested using a static water contact angle tester (Rame'-Hart instrument), and 5 ⁇ L of ultrapure water was slowly dropped vertically onto the sample surface by a syringe, and the machine's own imaging system was used to take a photograph of the droplet and analyze the contact. Angle size. Three pieces of material were used for each group, and five measurement data were averaged on each sample.
  • FIG. 4 is a graph showing the static contact angle of the surface of the polytetrafluoroethylene before and after the modification treatment in Example 1, wherein the abscissa is the sample name and the ordinate is the degree of the contact angle. It can be seen from Fig. 4 that the contact angle of the untreated PTFE control is 115°, and the contact angle is increased to 147° after the nitrogen plasma treatment. The ammonia gas plasma treatment reduces the contact angle to 42°, and the nitrogen plasma The surface contact angle after treatment with ammonia gas was approximately super-hydrophilic at 13°.
  • the modified polytetrafluoroethylene sample of Example 1 was immersed in a phosphate buffer solution containing heparin, wherein the concentration of heparin was 500 ⁇ g/mL, and stored at 4 ° C for 12 hours. The sample was then removed from the heparin solution and the sample was rinsed with heparin-free phosphate buffer to remove heparin that was not grafted.
  • the heparin loading on the surface of each sample was measured by toluidine blue colorimetric method, and the results shown in Fig. 5 were obtained, in which the abscissa is the sample name and the ordinate is the heparin loading density.
  • the untreated PTFE control cannot load heparin, and the sample ion-implanted by plasma immersion can effectively load heparin on the surface despite a certain difference in the load.
  • Example 6 After the modified polytetrafluoroethylene sample in Example 1 was stored in the air for 72 days or 198 days, the heparin loading was again incubated in the heparin solution according to the method of Example 5, and a graph was obtained.
  • the samples after the plasma treatment were stored in the air for half a year, their ability to load heparin in the heparin solution did not disappear, and the overall improvement was somewhat improved.
  • Example 5 The sample after heparin-loaded with nitrogen plasma in Example 5 was further immersed in a phosphate buffer solution containing no heparin, and stored at 37 ° C for a certain period of time, and then taken out, and the heparin loading amount on the surface was measured, and the result shown in FIG. As a result, the abscissa is the soaking time of the sample and the ordinate is the loading density of heparin.
  • the surface was treated with nitrogen plasma to have long-term stability. The surface heparin loading remained unchanged after soaking in phosphate buffer for up to 28 days. This aspect indicates that the loaded heparin has not been released, and on the other hand, heparin has not been denatured and inactivated during this process.
  • the modified polytetrafluoroethylene sample in Example 1 was immersed in a phosphate buffer solution containing horseradish peroxidase, wherein the horseradish peroxidase concentration was 50 ⁇ g/mL, and at 4 ° C Store under conditions for 12 hours. The sample was then removed from the solution and the sample was eluted with horseradish peroxidase-free phosphate buffered saline (PBS) for 1 hour or with 2% sodium lauryl sulfate (2% SDS). The sample was taken off for 1 hour.
  • PBS horseradish peroxidase-free phosphate buffered saline
  • SDS sodium lauryl sulfate
  • the eluted sample was then placed in a 24-well cell culture plate, and 500 ⁇ l of 3,3',5,5'-tetramethylbenzidine solution was added to each well and incubated for 3 minutes at room temperature, followed by 500 micron. A 2 mol/L hydrochloric acid solution was added to terminate the reaction. 200 ⁇ l of each well was taken out into a 96-well culture plate and the amount of horseradish peroxidase loaded on the surface of each sample was measured by measuring the absorbance at a wavelength of 450 nm on a microplate reader. The experimental results are shown in Fig. 8. In the figure, the abscissa is the elution method after incubation of each sample in horseradish peroxidase solution, and the ordinate is the absorbance at 450 nm.
  • the PTFE control sample which has not been subjected to plasma treatment can be loaded with a certain amount of horseradish peroxidase on its surface after being incubated for a while in the horseradish peroxidase solution.
  • the loaded enzyme can withstand the elution of phosphate buffer, the elution of sodium lauryl sulfate completely removes the enzyme supported on the surface, demonstrating that the enzyme supported on the PTFE control surface is only physically adsorbed on the surface of the material.
  • the enzyme loaded on the surface of the sample after each plasma treatment can be subjected to the elution of phosphate buffer and sodium lauryl sulfate, which proves that the enzyme is supported by covalent grafting because sodium lauryl sulfate is a kind.
  • the modified polytetrafluoroethylene sample in Example 1 was stored in air for 72 days or 198 days, and again incubated in the horseradish peroxidase solution according to the method of Example 8 and passed through the examples.
  • the method described in 8 detects the relative loading of horseradish peroxidase, and the results shown in Fig. 9 are obtained, wherein the abscissa is the storage time of the sample in air and the ordinate is the absorbance at 450 nm.
  • the samples after plasma treatment were stored in the air for half a year, their ability to covalently graft horseradish peroxidase by incubation did not decrease significantly.
  • a polyetheretherketone sheet having a diameter of 15 mm and a thickness of 2 mm was ultrasonically cleaned successively with acetone, alcohol, and deionized water. This pretreated sample is called PEEK control.
  • the pretreated polyetheretherketone is treated with oxygen plasma immersion ion implantation (O2PIII).
  • O2PIII oxygen plasma immersion ion implantation
  • the specific treatment process is as follows: the background vacuum is 5 ⁇ 10 -3 Pa, the gas introduction flow rate is 30 sccm, the sample disk is loaded with a negative bias voltage of 15 kV, the injection pulse width is 20 microseconds, the injection pulse frequency is 500 Hz, and the RF power is It is 1000W and the processing time is 180 minutes.
  • This treated sample is referred to as O2PIII.
  • the treated polyetheretherketone sample is immersed in a phosphate buffer solution containing horseradish peroxidase, wherein the horseradish is passed through
  • concentration of the oxide enzyme was 50 ⁇ g/mL, and it was stored at 4 ° C for 12 hours.
  • the sample was then removed from the solution and the sample was eluted with horseradish peroxidase-free phosphate buffered saline (PBS) for 1 hour or with 2% sodium lauryl sulfate (2% SDS). The sample was taken off for 1 hour.
  • PBS horseradish peroxidase-free phosphate buffered saline
  • SDS sodium lauryl sulfate
  • the eluted sample was then placed in a 24-well cell culture plate, and 500 ⁇ l of 3,3',5,5'-tetramethylbenzidine solution was added to each well and incubated for 3 minutes at room temperature, followed by 500 micron. A 2 mol/L hydrochloric acid solution was added to terminate the reaction. 200 ⁇ l of each well was taken out into a 96-well culture plate and the amount of horseradish peroxidase loaded on the surface of each sample was reflected by measuring the absorbance at a wavelength of 450 nm on a microplate reader. The experimental results are shown in Fig. 10. In the figure, the abscissa is the elution method after incubation of each sample in horseradish peroxidase solution, and the ordinate is the absorbance at 450 nm.
  • the surface-loaded enzyme of the plasma-free PEEK control sample can withstand the elution of phosphate buffer, but sodium lauryl sulfate.
  • the elution completely removes the enzyme loaded on the surface, proving that the enzyme is only physically adsorbed on the surface of the material.
  • the enzyme supported on the surface of the sample after O2PIII treatment was able to withstand the elution of phosphate buffer and sodium lauryl sulfate, which proved that the enzyme was supported by covalent grafting.

Abstract

公开了一种高分子材料的表面改性方法及其产品和用途，所述表面改性方法尤其涉及基于等离子体浸没离子注入处理医用高分子材料表面以及在处理后的表面共价接枝生物活性分子以实现其仿生化修饰；其具体包括如下步骤：1)通过气体等离子体浸没离子注入处理高分子材料；2)将处理过的高分子材料在含有生物分子的溶液中进行孵育。其中气体等离子体浸没离子注入表面改性的高分子材料稳定性好，即使长期保存在空气中，其接枝能力依然不会显著下降，并且其不使用化学交联剂；整个表面改性工艺过程简单、成本低廉、适用于批量及工业化生产。所述方法及其产品在医用植入材料、功能性材料、生物活性材料等领域具有广泛的应用前景。

Description

一种高分子材料表面改性方法及其产品和用途 技术领域
本发明涉及一种高分子材料的表面改性方法及其产品和用途，所述表面改性方法尤其涉及基于等离子体浸没离子注入处理医用高分子材料表面以及在处理后的表面共价接枝生物活性分子以实现其仿生化修饰。
背景技术
高分子材料也称为聚合物材料，在生物医用领域被广泛应用于生物体组织的修复、替代与再生，以及用作护理及医疗用具等。因其特殊的应用环境(需要直接与人体的体液、血液、器官、组织等接触)，生物医用高分子材料除了必须具有良好的物理机械性能、化学稳定性、无毒性、易加工成型性以外，还必须具有生物相容性、医用功能性等。由于医用高分子材料的生物学性能主要由其表面的物化性质所决定，对其进行表面改性可以在材料自身优点不受影响的前提下提高其生物学性能或者赋予其某些特殊的生物学功能。在众多表面改性方法中，对医用高分子材料进行仿生化修饰，即将具有生物活性的大分子如蛋白质、多糖、多肽、细胞生长因子等，通过共价接枝的方式负载在材料表面，能够使其表面形成一个能与生物环境特异性相互作用的稳定的生物化过渡层，以进一步提高材料的生物学性能或者赋予其特殊的生物学功能。例如，在聚四氟乙烯构建的人工血管表面接枝肝素、水蛭素等能够达到抑制血栓形成的效果，从而大大提高人工血管的远期通畅率(Hoshi R A,Van Lith R,Jen M C,et al.The blood and vascular cell compatibility of heparin-modified ePTFE vascular grafts.Biomaterials2013；34(1):30-41.Onder S,Kazmanli K,Kok F N.Alteration of PTFE surface to increase its blood compatibility.Journal of Biomaterials Science,Polymer Edition 2011；22(11):1443-14 57)。
然而，现有的进行仿生化修饰的方法一般是通过化学交联(chemical crosslinking)的方式将生物大分子接枝在材料表面(Kang E T,Zhang Y.Surface modification of fluoropolymers via molecular design.Advanced Materials 2000；12(20):1481-1494)。但是，有的高分子材料，比如聚四氟乙烯，具有优良的化学稳定性，因此很难单独通过化学方法对其进行表面改性。在此情况下，一般需要首先通过物理方法在材料表面引入一些功能基团，如氨基、羟基、羧基等，然后再通过化学交联的方式接枝负载生物大分子。另外，采用湿法化学交联技术不仅操作过程相对复杂繁琐，并且会引入具有毒性的有机交联试剂。更重要的是，这种化学方法很难同时在表面接枝多种生物活性分子，而顺序接枝多种生物分子又会使接枝过程极端繁琐甚至难以实现。
发明内容
本发明的目的在于提供一种简单可行的高分子材料表面改性仿生化修饰方法及其产品和用途，所述表面改性方法尤其涉及基于气体等离子体浸没离子注入(即气体PIII)处理医用高分子材料表面以及在处理后的表面共价接枝生物活性分子以实现其仿生化修饰。
本发明提供的改性方法无需使用化学交联剂，首先通过气体等离子体浸没离子注入对医用生物高分子材料进行表面改性和活化，然后将改性过的医用高分子材料浸泡在含有生物分子的溶液中孵育一段时间，即可将具有生物活性的大分子共价接枝负载在高分子材料表面，实现其仿生化表面修饰。
本发明中生物分子在医用材料表面的接枝原理为：在使用气体等离子体浸没离子注入技术对高分子材料进行改性的过程中，由注入的高能离子与高分子链的碰撞以及电荷和能量转移而在高分子材料表层产生大量具有长效性和很高活性的自由基(Free Radical)。这些由高能离子轰击形成的自由基能够长久地保存在离子注入的影响区，并不断地迁移到基体表面。到达表面的自由基与环境中存在的分子进行反应并且最终将分子共价接枝在材料表面。
本发明所采取的表面改性技术方案可分为两步：1.气体等离子体浸没离子注入处理；2.在含有生物分子溶液中的孵育。
1气体等离子体浸没离子注入
在进行注入时，所使用的样品盘上所加的是负偏压，这样可以将等离子体中带正电荷的离子加速吸引并最终使其注入到材料表层。
气体等离子体浸没离子注入所使用的工艺参数包括：本底真空度为5×10-4～9×10-3Pa，气体引入流量为10～200sccm，样品盘所加负偏压为5～50kV，注入脉宽为10～300微秒，注入脉冲频率为50～2000Hz，射频功率为100～3000W，注入时间为30～300分钟。
优选的参数为：本底真空度为1×10-3～9×10-3Pa，气体引入流量为20～100sccm，样品盘所加负偏压为10～30kV，注入脉宽为20～200微秒，注入脉冲频率为50～500Hz，射频功率为100～1000W，注入时间为30～180分钟。
最优选的参数为：本底真空度为5×10-3Pa，气体引入流量为30sccm，样品盘所加负偏压为15kV，注入脉宽为20微秒，注入脉冲频率为500Hz，射频功率为1000W，注入时间为60～180分钟。
一般而言，所述气体等离子体浸没离子注入中使用的气体无特殊要求，出于本发明的应用领域的需要，优选使用无毒的气体。
不同的气体可能会在某种程度上影响材料改性以后表面自由基的密度，从而影响接枝的效率，但是一般常见的气体如氧气、氮气、氩气、氨气、氢气等都具有运用于本发明的可行 性。
理论上此方法可以运用于所有能够经受气体PIII技术处理的高分子材料，例如聚乙烯、聚四氟乙烯、聚苯乙烯、聚氯乙烯、聚丙烯、聚酰胺、聚醚醚酮(polyetheretherketone，简称PEEK)、聚乳酸、聚乙醇酸、聚氨酯、聚(乳酸-羟基乙酸)共聚物、聚丁二酸丁二醇酯、聚已内酯、聚甲基丙烯酸甲酯、环氧树脂、、聚氯乙烯等。
作为一种经FDA测试认可的医用植入材料，聚醚醚酮具有不仅质轻、生物稳定性好且无生物毒性，更重要的是其弹性模量(5-8GPa)比金属骨科植入材料更接近人体骨骼，并且在植入体内后可被X射线透过、核磁共振成像和计算机断层扫描不会产生伪影等诸多生物医用优点。但是，PEEK是一种惰性的生物材料，生物相容性的不足导致其在植入后与相邻骨组织的结合(Osseointegration)不够充分而需要二次手术进行修正。
此外，如上所述，聚四氟乙烯，具有优良的化学稳定性，因此很难单独通过化学方法对其进行表面改性。
因此，考虑到其在医用高分子材料领用的使用潜力，本发明中的高分子材料优选聚四氟乙烯、聚醚醚酮。
2含有生物分子溶液中的孵育
即，将通过气体等离子体浸没离子注入处理过的高分子材料在含有生物分子的溶液中进行孵育。
其中，含有生物分子的溶液为能够使生物分子保持活性的缓冲液体系，比如磷酸盐缓冲液(PBS)或生理盐水等。
在含有生物分子的溶液中孵育的温度和时间需保证孵育期间生物分子能够保持生物活性。孵育的温度通常选择在4-37℃；孵育的时间保证接枝完成即可；优选的条件例如在含有生物分子的溶液中于4℃条件下孵育12小时以上。
此外，可以通过孵育时所使用的生物溶液的浓度来调节生物分子在高分子材料表面的负载量，所述生物溶液的浓度例如为10-2000μg/mL，优选50-500μg/mL。
可以通过在相应生物分子的共混合溶液中孵育一段时间来实现同时负载两种及以上的生物分子。
也可以在通过气体等离子体浸没离子注入处理过的高分子材料的不同部位接枝不同的生物分子来进一步实现所述高分子材料的多样功能化的需求，所述在材料的不同部位接枝不同的生物分子可以依此进行，或者通过将不同部位分隔，以相应的不同的生物分子溶液孵育来一次或多次地完成接枝。
不同生物分子的接枝能够实现不同的功能，所述生物分子可为多糖(如肝素)、多肽(如水蛭素)、蛋白质(如辣根过氧化物酶、跨膜糖蛋白CD47)、细胞因子(如人基质细胞衍生因子1α(SDF-1α))等。
气体等离子体浸没离子注入处理的高分子材料表面在保存在空气中的情况下，其通过在含有生物分子的溶液中孵育即可共价负载生物分子的能力具有长期有效性。
根据本发明的方法得到的表面以生物分子修饰的高分子材料，其具有如下结构：高分子材料的表层存在通过气体等离子体浸没离子注入方式引入的活性自由基，其与生物分子反应并将后者共价接枝在材料表面。
本发明的有益效果
综上所述，本发明采用气体等离子体浸没离子注入技术处理生物医用高分子材料，在无需使用化学交联剂的情况下即可实现将具有生物活性的大分子共价接枝负载在材料表面，实现其仿生化表面修饰。与现有技术相比，本发明具备以下优点：
1.等离子体浸没离子注入技术消除了传统束线离子注入的“视线限制”，注入过程是全方位的，即使是形态复杂的试样也可以均匀地进行表面处理。
2.等离子体浸没离子注入处理在不影响高分子材料基体性能的前提下，能够极大地改善其表面物化性质，如表面粗糙度，表面能，表面化学成分等。并且运用不同的气体进行注入处理，能得到不同的表面物化性质。
3.等离子体浸没离子注入处理以后的高分子材料，其表面无需化学交联剂处理，仅需浸入到含有生物分子的溶液中孵育一段时间，即可将溶液中的生物活性分子共价负载在材料表面。此表面修饰方法不但操作简单方便，更避免了毒性化学交联剂的使用，有利于大批量、工业化生产。
4.生物分子在高分子材料表面的负载量可以通过孵育所使用的溶液的浓度进行调节。并且当使用多种生物分子的共混合溶液时，相应的多种生物分子均能共价接枝到等离子体浸没离子注入处理过后的高分子材料表面。
5.气体等离子体浸没离子注入表面改性的高分子材料对处理后的保存条件无特殊要求。即使长期保存在空气中，其通过在含有生物分子的溶液中孵育即可共价接枝生物分子的能力依然不会显著下降。
本发明提供的生物医用高分子材料表面仿生化修饰方法在医用植入材料、功能性材料、生物活性材料等领域具有广泛的应用前景，并且其工艺过程简单、成本低廉、适用于批量及工业化生产。
附图说明
图1a是实施例1中未经等离子体浸没离子注入处理的聚四氟乙烯表面的扫描电镜图。
图1b是实施例1中经氮气等离子体浸没离子注入处理的聚四氟乙烯表面的扫描电镜图。
图1c是实施例1中经氨气等离子体浸没离子注入处理的聚四氟乙烯表面的扫描电镜图。
图1d是实施例1中经氮气注入以后再经氨气等离子体浸没离子注入处理的聚四氟乙烯表面的扫描电镜图。
图2a是实施例2中未经等离子体浸没离子注入处理的聚四氟乙烯表面的原子力显微镜表征三维图片、剖面轮廓以及其对应的均方根粗糙度(RMS)。
图2b是实施例2中经氮气等离子体浸没离子注入处理的聚四氟乙烯表面的原子力显微镜表征三维图片、剖面轮廓以及其对应的均方根粗糙度(RMS)。
图2c是实施例2中经氨气等离子体浸没离子注入处理的聚四氟乙烯表面的原子力显微镜表征三维图片、剖面轮廓以及其对应的均方根粗糙度(RMS)。
图2d是实施例2中经氮气注入后再经氨气等离子体浸没离子注入处理的聚四氟乙烯表面的原子力显微镜表征三维图片、剖面轮廓以及其对应的均方根粗糙度(RMS)。
图3是实施例3中气体等离子体浸没离子注入处理前后的聚四氟乙烯材料表面的X射线光电子能谱全谱谱图。
图4是实施例4中气体等离子体浸没离子注入处理前后的聚四氟乙烯材料表面静态接触角结果。
图5是实施例5中经气体等离子体浸没离子注入处理前后的试样在肝素溶液中孵育后其表面的肝素负载密度。
图6是实施例6中经气体等离子体浸没离子注入处理后的试样在空气中保存相应时间后再在肝素溶液中孵育后的表面肝素负载密度。
图7是实施例7中肝素在氮气等离子体浸没离子注入处理的聚四氟乙烯表面的长效稳定性。
图8是实施例8中经各气体等离子体浸没离子注入处理及未经处理的表面在负载辣根过氧化物酶以后经磷酸盐缓冲液或者2％十二烷基硫酸钠洗脱以后其表面辣根过氧化物酶的留存量。
图9是实施例9中经各气体等离子体浸没离子注入处理后的试样在空气中保存相应时间后再次负载辣根过氧化物酶并经2％十二烷基硫酸钠洗脱以后其表面辣根过氧化物酶的留存量。
图10是实施例10中经氧气等离子体浸没离子注入处理及未经处理(PEEK control)的表 面在负载辣根过氧化物酶以后经磷酸盐缓冲液或者2％十二烷基硫酸钠洗脱以后其表面辣根过氧化物酶的留存量。
具体实施方式
实施例1
将直径15mm，厚0.1mm的聚四氟乙烯薄片依次用丙酮、酒精、去离子水超声清洗干净。该预处理后的样品称为PTFE control。
采用气体等离子体浸没离子注入技术处理经预处理的聚四氟乙烯。运用氮气注入、氨气注入、或者氮气注入以后再次注入氨气的方法来进行处理。具体处理工艺为：本底真空度为5×10-3Pa，气体的引入流量为30sccm，样品盘所加负偏压为15kV，注入脉宽为20微秒，注入脉冲频率为500Hz，射频功率为1000W。其中，氮气的注入时间为180分钟，该处理后的样品称为N2PIII；氨气的注入时间为60分钟，该处理后的样品称为NH3PIII；注入氮气180分钟后再注入氨气注入60分钟，该处理后的样品称为N2+NH3PIII。(下同)
通过扫描电子显微镜对气体等离子体浸没离子注入处理前后的聚四氟乙烯表面进行观察，得到图1所示的表面微观形貌照片。由图1可知，气体等离子体浸没离子注入处理不同程度地改变了聚四氟乙烯的表面形貌。图1a所示未经处理的PTFE control表面基本平整，而图1b所示的氮气等离子体注入以后的N2PIII试样表面呈现出准规则的纳米级别“谷峰”状结构。图1c所示的氨气等离子体注入处理以后的NH3PIII试样表面与PTFE control表面相似，而图1d所示的氮气注入后再进行氨气注入的N2+NH3PIII试样表面与N2PIII表面相似，证明氨气等离子体注入未改变聚四氟乙烯的表面形貌。
实施例2
采用原子力显微镜对实施例1中处理得到的聚四氟乙烯样品的表面粗糙度进行表征，得到图2所示表面三维图片、剖面轮廓以及对应的均方粗糙度(RMS)结果。由图2中的表面三维图片可知原子力显微镜所得结果与实施例1中扫描电镜所得表面形貌基本一致。图2a所示PTFE control的表面均方粗糙度为17.9nm。氮气等离子体注入显著地将试样的表面粗糙度提高到134nm(图2b)。氨气等离子体注入对表面粗糙度基本没有影响，其处理后的均方粗糙度为18.2nm(图2c)。氮气等离子体注入后再进行氨气注入的表面均方粗糙度与氮气单独处理的表面基本一致，为130nm(图2d)。
实施例3
对实施例1中处理得到的聚四氟乙烯样品表面进行X射线光电子能谱(XPS)宽场扫描，得到图3所示的XPS全谱谱图。其中横坐标表示结合能，纵坐标表示峰强。通过观察图3中各试样的C 1s峰、O 1s峰、N 1s峰以及F 1s峰的峰高可知，氮气等离子体浸没离子注入处 理一定程度上减少了聚四氟乙烯表面的氟元素含量，并在材料表面引入了氧元素；而氨气等离子体浸没离子注入处理显著减少了表面氟元素的含量，并且显著增加了表面氮元素以及氧元素的比例。
实施例4
采用静态水接触角测试仪(Rame’-Hart instrument)测试材料表面润湿性，通过注射器将5μL超纯水垂直慢速悬滴到样品表面，使用机器自带成像系统拍摄液滴照片并分析接触角大小。每组材料3片，在每个样品上取5个测量数据求平均值。
图4是实施例1中的改性处理前后聚四氟乙烯表面的静态接触角实验图，横坐标为样品名称，纵坐标为接触角的度数。由图4可知，未经处理的PTFE control的接触角为115°，氮气等离子体处理后其接触角增大到147°.而氨气等离子体处理使其接触角降低到42°，氮气等离子体处理以后再用氨气处理的表面接触角近似超亲水，为13°。
实施例5
将实施例1中改性处理后的聚四氟乙烯试样浸入到含有肝素的磷酸盐缓冲溶液中，其中肝素的浓度为500μg/mL，并在4℃条件下保存12小时。然后将试样从肝素溶液中取出，用不含肝素的磷酸盐缓冲液漂洗试样，去除未接枝上的肝素。运用甲苯胺蓝比色法检测各试样表面的肝素负载量，得到图5所示结果，其中横坐标为样品名称，纵坐标为肝素的负载密度。由图5可知，未经处理的PTFE control并不能负载肝素，而经等离子体浸没离子注入的样品，虽负载量有一定的差别，都能够有效地将肝素负载在其表面。
实施例6
将实施例1中改性处理后的聚四氟乙烯试样保存在空气中72天或者198天以后，再次按照实施例5中的方法，在肝素溶液中孵育并检测肝素的负载量，得到图6所示结果，其中横坐标为样品在空气中的保存时间，纵坐标为肝素的负载密度。由图6可知，虽然等离子体处理以后的样品存放在空气中长达半年时间，它们通过孵育在肝素溶液中负载肝素的能力并没有消失，总体反而有一定程度的提高。
实施例7
将实施例5中氮气等离子体处理的负载肝素以后的试样继续浸入不含肝素的磷酸盐缓冲液中，保存在37℃一定时间后取出，检测其表面的肝素负载量，得到图7所示结果，其中横坐标为样品的浸泡时间，纵坐标为肝素的负载密度。由图7可知，经过肝素负载在氮气等离子体处理表面以后具有长效稳定性。在浸泡在磷酸盐缓冲液中长达28天以后，其表面肝素的负载量依然没有变化。这一方面说明所负载的肝素并没有被释放出来，另一方面也说明肝素在此过程中并没有变性失活。
实施例8
将实施例1中改性处理后的聚四氟乙烯试样浸入到含有辣根过氧化物酶的磷酸盐缓冲溶液中，其中辣根过氧化物酶的浓度为50μg/mL，并在4℃条件下保存12小时。然后将试样从溶液中取出，用不含辣根过氧化物酶的磷酸盐缓冲液(PBS)洗脱试样1小时，或者用2％的十二烷基硫酸钠(2％SDS)洗脱试样1小时。然后将洗脱后的试样放入24孔细胞培养板，每孔添加500微升3,3’,5,5’-四甲基联苯胺溶液并在室温中孵育3分钟，随后添加500微升2mol/L的盐酸溶液以终止反应。从每孔中取出200微升放入96孔培养板中并通过在酶标仪上测量其在450nm波长处的吸光度来反应各试样表面辣根过氧化物酶的负载量。实验结果如图8所示，图中：横坐标为各试样在辣根过氧化物酶溶液中孵育后的洗脱方法，纵坐标为450nm下的吸光度。
由图8可知，没有经过等离子体处理的PTFE control试样在辣根过氧化物酶溶液中孵育一段时间以后，在其表面能够负载一定量的辣根过氧化物酶。负载的酶虽能够经受磷酸盐缓冲液的洗脱，但是十二烷基硫酸钠的洗脱能够完全清除表面所负载的酶，证明在PTFE control表面负载的酶只是通过物理方式吸附在材料表面。而各等离子体处理以后试样表面负载的酶能够经受磷酸盐缓冲液以及十二烷基硫酸钠的洗脱，证明酶的负载方式是共价接枝，因为十二烷基硫酸钠是一种阴离子活性剂，能够破坏蛋白与材料之间物理吸附作用力，而不能破坏它们之间的化学接枝。
实施例9
将实施例1中改性处理后的聚四氟乙烯试样保存在空气中72天或者198天以后，再次按照实施例8中的方法，在辣根过氧化物酶溶液中孵育并通过实施例8中所述方法检测辣根过氧化物酶的相对负载量，得到图9所示结果，其中横坐标为样品在空气中的保存时间，纵坐标为450nm下的吸光度。由图9可知，虽然等离子体处理以后的样品存放在空气中长达半年时间，它们通过孵育的方式共价接枝辣根过氧化物酶的能力并没有明显下降。
实施例10
将直径15mm，厚2mm的聚醚醚酮薄片依次用丙酮、酒精、去离子水超声清洗干净。该预处理后的样品称为PEEK control。
利用氧气等离子体浸没离子注入(O2PIII)处理经预处理的聚醚醚酮。具体处理工艺为：本底真空度为5×10-3Pa，气体的引入流量为30sccm，样品盘所加负偏压为15kV，注入脉宽为20微秒，注入脉冲频率为500Hz，射频功率为1000W，处理时间为180分钟。该处理后的样品称为O2PIII。
将处理后的聚醚醚酮试样浸入到含有辣根过氧化物酶的磷酸盐缓冲溶液中，其中辣根过 氧化物酶的浓度为50μg/mL，并在4℃条件下保存12小时。然后将试样从溶液中取出，用不含辣根过氧化物酶的磷酸盐缓冲液(PBS)洗脱试样1小时，或者用2％的十二烷基硫酸钠(2％SDS)洗脱试样1小时。然后将洗脱后的试样放入24孔细胞培养板，每孔添加500微升3,3’,5,5’-四甲基联苯胺溶液并在室温中孵育3分钟，随后添加500微升2mol/L的盐酸溶液以终止反应。从每孔中取出200微升放入96孔培养板中并通过在酶标仪上测量其在450nm波长处的吸光度来反映各试样表面辣根过氧化物酶的负载量。实验结果如图10所示，图中：横坐标为各试样在辣根过氧化物酶溶液中孵育后的洗脱方法，纵坐标为450nm下的吸光度。
由图10可知，与PTFE表面辣根过氧化物酶的结果相似，没有经过等离子体处理的PEEK control试样表面负载的酶虽能够经受磷酸盐缓冲液的洗脱，但是十二烷基硫酸钠的洗脱能够完全清除表面所负载的酶，证明酶只是通过物理方式吸附在材料表面。而O2PIII处理以后试样表面负载的酶能够经受磷酸盐缓冲液以及十二烷基硫酸钠的洗脱，证明酶的负载方式是共价接枝。

Claims (16)

  1. 一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，包括如下步骤：
    1)通过气体等离子体浸没离子注入处理高分子材料；
    2)将处理过的高分子材料在含有生物分子的溶液中进行孵育；
    从而将生物分子以共价的形式接枝到高分子材料的表面，其中，所述气体选自无毒的气体；所述高分子材料选自能够经受等离子体浸没离子注入技术处理的高分子材料。
  2. 根据权利要求1所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述高分子材料选自聚乙烯、聚四氟乙烯、聚苯乙烯、聚氯乙烯、聚丙烯、聚酰胺、聚醚醚酮、聚乳酸、聚乙醇酸、聚氨酯、聚(乳酸-羟基乙酸)共聚物、聚丁二酸丁二醇酯、聚已内酯、聚甲基丙烯酸甲酯、环氧树脂。
  3. 根据权利要求1所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述生物分子选自多糖、多肽、蛋白质、细胞因子。
  4. 根据权利要求3所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述多糖选自肝素，多肽选自水蛭素，蛋白质选自辣根过氧化物酶或跨膜糖蛋白CD47，细胞因子选自人基质细胞衍生因子1α。
  5. 根据权利要求1或2所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述等离子体浸没离子注入处理所使用的气体选自氩气、氮气、氨气、氧气、氢气。
  6. 根据权利要求1或2所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述等离子体浸没离子注入处理中本底真空度为1×10-3～9×10-3Pa，气体引入流量为20～100sccm，样品盘所加负偏压为10～30kV。
  7. 根据权利要求6所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述等离子体浸没中本底真空度为5×10-3Pa，气体引入流量为30sccm，样品盘所加负偏压为15kV，注入脉宽为20微秒，注入脉冲频率为500Hz，产生等离子体所使用的射频功率为1000W，注入时间为60～180分钟。
  8. 根据权利要求1或3所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述含有生物分子的溶液为溶解了生物分子并能使其保持活性的缓冲液体系，在含有生物分子的溶液中孵育的温度和时间需保证孵育期间生物分子能够保持生物活性。
  9. 根据权利要求8所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述使生物分子保持活性的缓冲液体系选自磷酸盐缓冲液或生理盐水。
  10. 根据权利要求8所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述处理过的高分子材料在含有生物分子的溶液中的孵育是指将具有生物活性的大分子溶解在磷酸盐缓冲液中，并在4℃条件下孵育12小时以上。
  11. 根据权利要求8所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，所述生物分子在等离子体浸没离子注入处理后的高分子材料表面的负载量通过孵育时所使用的生物溶液的浓度来调节，以及生物溶液的浓度为10-2000μg/mL之间。
  12. 根据权利要求8所述的一种基于等离子体浸没离子注入技术的高分子材料表面改性方法，其特征在于，通过在两种及以上生物分子的共混合溶液中孵育一段时间实现相应的生物分子在等离子体浸没离子注入处理后的高分子材料表面的同时负载。
  13. 一种表面以生物分子共价接枝修饰的高分子材料，其特征在于，使用上述任一项权利要求中的生物分子及高分子材料，且所述生物分子在高分子材料表面上的共价接枝根据相应上述任一项权利要求所述的方法制备。
  14. 权利要求13所述的一种表面以生物分子共价接枝修饰的高分子材料的用途，其特征在于：用于生物医用材料。
  15. 根据权利要求14所述的高分子材料的用途，其特征在于：用于医用植入材料、医用功能性材料、医用生物活性材料。
  16. 一种表面以生物分子共价接枝修饰的高分子材料，其特征在于，所述高分子材料选自能够经受等离子体浸没离子注入技术处理的高分子材料，优选聚四氟乙烯、聚醚醚酮；所述生物分子选自多糖、多肽、蛋白质、细胞因子，优选肝素、辣根过氧化物酶。
PCT/CN2017/084811 2017-04-28 2017-05-18 高分子材料表面改性方法及其产品和用途 WO2018196055A1 (zh)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
CN201710295567.XA CN107189096B (zh) 2017-04-28 2017-04-28 一种高分子材料表面改性方法及其产品和用途
CN201710295567.X 2017-04-28

Publications (1)

Publication Number Publication Date
WO2018196055A1 true WO2018196055A1 (zh) 2018-11-01

Family

ID=59872345

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2017/084811 WO2018196055A1 (zh) 2017-04-28 2017-05-18 高分子材料表面改性方法及其产品和用途

Country Status (2)

Country Link
CN (1) CN107189096B (zh)
WO (1) WO2018196055A1 (zh)

Families Citing this family (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN108424535B (zh) * 2018-03-30 2021-03-30 南京腾逸新材料科技有限公司 一种经过低温等离子体处理的极性聚合物粉体
CN109847807B (zh) * 2019-03-21 2022-04-08 青岛大学 基于等离子体处理和原位沉积法的脱硝滤料及其制备方法
CN109847580B (zh) * 2019-03-21 2022-04-08 青岛大学 基于等离子体前处理和浸渍法的脱硝滤料及其制备方法
CN110180037A (zh) * 2019-05-17 2019-08-30 西南交通大学 一种在无机医疗器械表面获得产生活性自由基和基团活性表面层的方法
EP4041882A1 (en) * 2019-10-11 2022-08-17 Regenhu AG Method for covalent immobilization of molecular compounds
CN111494704B (zh) * 2020-04-14 2022-01-25 李贺杰 制备小肽涂层的镁基合金生物材料的方法及其应用
CN113750290A (zh) * 2020-06-03 2021-12-07 深圳先进技术研究院 聚醚醚酮复合植入物及其制备方法和应用
CN113769167B (zh) * 2021-09-14 2023-07-25 深圳先进技术研究院 一种可顺序释放生物活性因子的骨科植入材料的制备方法及其产品和用途
CN114106493B (zh) * 2022-01-24 2022-04-29 山东大学 一种肝素化pvc材料、其制备方法及作为医疗器械的应用
CN116212084A (zh) * 2023-02-01 2023-06-06 中国科学院深圳先进技术研究院 具有双重抗菌功效的可降解伤口敷料及其制备方法和应用
CN117467929B (zh) * 2023-12-28 2024-03-26 核工业西南物理研究院 一种高分子材料表面金属化处理方法

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101214395A (zh) * 2008-01-02 2008-07-09 西南交通大学 一种无机材料表面生物化的方法
US20100227372A1 (en) * 2007-07-27 2010-09-09 The University Of Sydney Biological functionalisation of substrates
CN101927037A (zh) * 2009-12-10 2010-12-29 西南交通大学 一种抗凝血的血管支架的制备方法
CN103865084A (zh) * 2014-04-09 2014-06-18 中国科学院上海硅酸盐研究所 一种聚醚醚酮材料及其表面改性的方法

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070191931A1 (en) * 2006-02-16 2007-08-16 Jan Weber Bioerodible endoprostheses and methods of making the same
CN101987223B (zh) * 2009-07-29 2013-03-27 山东百多安医疗器械有限公司 具有抗凝抗菌功能的多向瓣膜经外周中心静脉导管及其制备方法

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100227372A1 (en) * 2007-07-27 2010-09-09 The University Of Sydney Biological functionalisation of substrates
CN101214395A (zh) * 2008-01-02 2008-07-09 西南交通大学 一种无机材料表面生物化的方法
CN101927037A (zh) * 2009-12-10 2010-12-29 西南交通大学 一种抗凝血的血管支架的制备方法
CN103865084A (zh) * 2014-04-09 2014-06-18 中国科学院上海硅酸盐研究所 一种聚醚醚酮材料及其表面改性的方法

Also Published As

Publication number Publication date
CN107189096B (zh) 2020-05-22
CN107189096A (zh) 2017-09-22

Similar Documents

Publication Publication Date Title
WO2018196055A1 (zh) 高分子材料表面改性方法及其产品和用途
US6387379B1 (en) Biofunctional surface modified ocular implants, surgical instruments, medical devices, prostheses, contact lenses and the like
EP0611792B1 (en) Graft polymerization
Poncin-Epaillard et al. Surface engineering of biomaterials with plasma techniques
Gomathi et al. RF plasma-treated polymers for biomedical applications
Ratner et al. Plasma deposition and treatment for biomaterial applications
Hsu et al. Improved cell adhesion by plasma-induced grafting of L-lactide onto polyurethane surface
Yoshida et al. Surface modification of polymers by plasma treatments for the enhancement of biocompatibility and controlled drug release
US5080924A (en) Method of making biocompatible, surface modified materials
Ratner Plasma deposition for biomedical applications: a brief review
US5236563A (en) Surface-modified bioabsorbables
AU713357B2 (en) Medical device with biomolecule-coated surface graft matrix
CN101214395A (zh) 一种无机材料表面生物化的方法
Jamesh et al. Evaluation of corrosion resistance and cytocompatibility of graded metal carbon film on Ti and NiTi prepared by hybrid cathodic arc/glow discharge plasma-assisted chemical vapor deposition
CN107921177A (zh) 制备组织工程用三维聚合物支架的方法
Kim et al. Effect of poly (ethylene glycol) graft polymerization of poly (methyl methacrylate) on cell adhesion: In vitro and in vivo study
Junkar Interaction of cells and platelets with biomaterial surfaces treated with gaseous plasma
Eloy et al. In vitro evaluation of inflammatory cell response after CF4 plasma surface modification of poly (methyl methacrylate) intraocular lenses
Poulsson et al. Surface modification techniques of polyetheretherketone, including plasma surface treatment
Chudinov et al. Polyurethane modified with plasma-ion implantation for medical applications
Klapperich et al. Chemical and biological characteristics of low-temperature plasma treated ultra-high molecular weight polyethylene for biomedical applications
Vasilets et al. Regulation of the biological properties of medical polymer materials with the use of a gas-discharge plasma and vacuum ultraviolet radiation
KR20180112697A (ko) 선택적 플라즈마 에칭법에 의해 금속화된 표면을 갖는 의료용 고분자 및 이의 제조방법
Mahmoodi et al. In vitro evaluation of collagen immobilization on polytetrafluoroethylene through NH 3 plasma treatment to enhance endothelial cell adhesion and growth
EP3206728A1 (en) Method of growing carbon nanowalls on a substrate

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 17907945

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 17907945

Country of ref document: EP

Kind code of ref document: A1

32PN Ep: public notification in the ep bulletin as address of the adressee cannot be established

Free format text: NOTING OF LOSS OF RIGHTS PURSUANT TO RULE 112(1) EPC (EPO FORM 1205A DATED 28.08.2020)

122 Ep: pct application non-entry in european phase

Ref document number: 17907945

Country of ref document: EP

Kind code of ref document: A1