CN108525023B - Application of pure magnesium/coating composite material and preparation method thereof - Google Patents

Application of pure magnesium/coating composite material and preparation method thereof Download PDF

Info

Publication number
CN108525023B
CN108525023B CN201810385486.3A CN201810385486A CN108525023B CN 108525023 B CN108525023 B CN 108525023B CN 201810385486 A CN201810385486 A CN 201810385486A CN 108525023 B CN108525023 B CN 108525023B
Authority
CN
China
Prior art keywords
pure magnesium
coating
magnesium
composite material
dcpd
Prior art date
Legal status (The legal status 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 status listed.)
Active
Application number
CN201810385486.3A
Other languages
Chinese (zh)
Other versions
CN108525023A (en
Inventor
李翔骥
王勇
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Third Affiliated Hospital Of Cqmu (gener Hospital)
Chongqing University
Original Assignee
Third Affiliated Hospital Of Cqmu (gener Hospital)
Chongqing University
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 Third Affiliated Hospital Of Cqmu (gener Hospital), Chongqing University filed Critical Third Affiliated Hospital Of Cqmu (gener Hospital)
Priority to CN201810385486.3A priority Critical patent/CN108525023B/en
Publication of CN108525023A publication Critical patent/CN108525023A/en
Application granted granted Critical
Publication of CN108525023B publication Critical patent/CN108525023B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/148Materials at least partially resorbable by the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/02Inorganic materials
    • A61L31/022Metals or alloys
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08Materials for coatings
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/08Materials for coatings
    • A61L31/082Inorganic materials
    • A61L31/086Phosphorus-containing materials, e.g. apatite
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L31/16Biologically active materials, e.g. therapeutic substances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/10Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing inorganic materials
    • A61L2300/102Metals or metal compounds, e.g. salts such as bicarbonates, carbonates, oxides, zeolites, silicates
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2300/00Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/602Type of release, e.g. controlled, sustained, slow
    • A61L2300/604Biodegradation
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2420/00Materials or methods for coatings medical devices
    • A61L2420/02Methods for coating medical devices

Abstract

The invention relates to an application of a pure magnesium/coating composite material in preparing a glaucoma drainage device, the glaucoma drainage device made of the pure magnesium/coating composite material can be degraded and absorbed by tissues after operation, the proliferation of Tenon's capsule fibroblasts can be fully inhibited, the generation of scars can be reduced, and magnesium ions released in the degradation process can play a role in protecting optic nerves. Compared with the traditional titanium alloy, the pure magnesium/coating composite material has obviously lower cytotoxicity to fibroblasts, effectively inhibits the proliferation of Tenon's fibroblasts, reduces the expression of specific protein a-SMA, and has the effect of inhibiting the activity of fibroblasts.

Description

Application of pure magnesium/coating composite material and preparation method thereof
Technical Field
The invention belongs to the technical field of medical implant materials, and relates to application of a pure magnesium/coating composite material and a preparation method thereof.
Background
Glaucoma is the second leading cause of blindness and is also the leading cause of irreversible blindness rates worldwide. China is the country with the most population in the world, glaucoma is one of the leading blindness eye diseases in China, and the influence caused by visual dysfunction and blindness caused by glaucoma is not negligible. Over the last decade, minimally invasive glaucoma surgery has emerged, surgery being an important treatment option for glaucoma, and recently implanted devices, the most advanced surgery in the world for the treatment of various forms of glaucoma, particularly refractory glaucoma. The first generation of microcutting devices were made of titanium, and since then other materials were introduced.
However, glaucoma drainage implant surgery can be associated with as many as 20 or more complications, with at least one complication occurring in about 60% to 70%. Although partly attributed to the complex nature of the eye selected for implantation surgery, many complications arise from deficiencies in drainage device design and materials. The traditional glaucoma drainage device is permanently arranged under the conjunctiva, and the inflammation easily caused by foreign matters causes the postoperative cicatrization. Traditional titanium alloys cause fibroblast proliferation, fibrosis and fistula blockage due to the sustained action of inflammatory mediators and cytokines at the level of the Tenon's capsule-sclera interface. Therefore, the adoption of new biodegradable materials with good biocompatibility in glaucoma surgery still leaves great room for research on auxiliary methods for reducing subconjunctival space scars, reducing inflammation, and slowing or stopping the healing process of excessive fibrosis. The current situation for glaucoma drainage devices is similar to that of intraocular lenses in the early 70's of the 19 th century. Are frequently accompanied by complications due to design and material deficiencies. Just as the improved intraocular lens has promoted the rapid development of cataract surgery over the past decades, the development of biodegradable materials that can effectively reduce fibroblast proliferation, reduce specific protein expression and RNA replication and further applied to the skillfully designed glaucoma drainage device may open a new era of drainage implantation surgery.
Disclosure of Invention
In view of the above, the present invention aims to provide an application of a pure magnesium/coating composite material in the preparation of a glaucoma drainage device
In order to achieve the purpose, the invention provides the following technical scheme:
1. the application of the pure magnesium/coating composite material in the preparation of glaucoma drainage devices.
Further, the coating is hydroxyapatite, calcium phosphorus or calcium phosphorus-stearic acid.
Further, the pure magnesium is 99.99% magnesium.
Further, the thickness of the coating is 2-4 μm.
2. The preparation method of the pure magnesium/coating composite material in the application comprises the following steps:
a. carrying out hot extrusion on pure magnesium, polishing the surface of the pure magnesium by using sand paper, then carrying out ultrasonic cleaning, and drying;
b. and then it is formed into a coating using electrodeposition and conversion coating methods.
Further, the hot extrusion process comprises the following steps: the extrusion temperature is 170-180 ℃, and the extrusion ratio is 20-25.
The bulk to pressure ratio is the ratio of the cross-sectional areas of the material before and after extrusion.
Further, the sand paper is 320-.
Further, the ultrasonic cleaning uses acetone or ethanol.
The invention has the beneficial effects that: the glaucoma drainage device made of the pure magnesium/coating composite material can be automatically degraded and absorbed by tissues after operation, the proliferation of Tenon's capsule fibroblasts can be fully inhibited, the generation of scars can be reduced, and magnesium ions released in the degradation process can play a role in protecting optic nerves. Compared with the traditional titanium alloy, the pure magnesium/coating composite material has obviously lower cytotoxicity to fibroblasts, effectively inhibits the proliferation of Tenon's fibroblasts, reduces the expression of specific protein a-SMA, and has the effect of inhibiting the activity of fibroblasts.
Drawings
In order to make the object, technical scheme and beneficial effect of the invention more clear, the invention provides the following drawings for explanation:
FIG. 1 is an SEM image of a pure magnesium/HA coating;
FIG. 2 is an SEM image of a pure magnesium/DCPD coating;
FIG. 3 is an SEM image of a pure magnesium/DCPD + SA coating;
FIG. 4 is a magnified image of a DCPD coating at 100x (A) and 1000x (B);
FIG. 5 is a magnified image of a DCPD + SA coating at 100x (C) and 500x (D);
fig. 6 is a 2000x magnified image of the HA coating;
FIG. 7 is a graph of pH change in balanced salt solution for each sample;
FIG. 8 is a graph of the weight change of each sample in balanced salt solution;
FIG. 9 is a graph showing the variation of the concentration of magnesium ions in the balanced salt solution of each group of samples;
FIG. 10 is a graph showing the variation of the calcium ion concentration in the balanced salt solution of each group of samples;
FIG. 11 is a graph showing the change in the concentration of phosphorus ions in the balanced salt solution of each group of samples;
FIG. 12 is a graph of the change in metabolic activity of HTCFs treated with various groups of samples;
FIG. 13 is a graph of the change in cytotoxicity of HTCFs treated with various groups of samples;
FIG. 14 relative proliferation rates of different coatings of pure magnesium versus HTCFs;
FIG. 15 effect of pure magnesium on a-SMA expression for different coatings.
Detailed Description
Preferred embodiments of the present invention will be described in detail below with reference to the accompanying drawings. The experimental procedures, in which specific conditions are not specified in the examples, are generally carried out under conventional conditions or under conditions recommended by the manufacturers.
Materials: pure magnesium with a purity of 99.99% is provided by the national magnesium alloy engineering research center of Chongqing university.
EXAMPLE 1 pure magnesium/HA coated composite
a. Pure magnesium was extruded into a rod at 170 ℃ under an extrusion ratio of 20, and then cut into a wafer having a diameter of 14.5mm and a thickness of 1mm, and the surface of the wafer was polished using 320-. All discs were ultrasonically cleaned in acetone, air dried and weighed.
b. Then, the HA coating is formed by using an electrodeposition and conversion coating method, and the electrolyte is 0.042mol/L (Ca (NO)3)2) And 0.025mol/L (NH)4H2PO4) The aqueous solution of (1) and the coating layer had a CA/P ratio of 1.67, a pH of 5.0, an electrolytic voltage of 3V, and a deposition time of 4 hours and a thickness of 2 μm.
SEM images of pure magnesium/HA coatings are shown in FIG. 1, where Ai is 100 times and Aii is 1000 times.
EXAMPLE 2 pure magnesium/DCPD coating composite
a. Pure magnesium was extruded into a rod at 180 ℃ and an extrusion ratio of 25, and then cut into a wafer having a diameter of 14.5mm and a thickness of 1mm, and the surface of the wafer was polished using 320 and 800# sandpaper. All discs were ultrasonically cleaned in acetone, air dried and weighed.
b. The DCPD coating is formed by electrodeposition and conversion coating, and the electrolyte is 3.1% disodium hydrogen phosphate (Na)2HPO4) and 5.3% calcium nitrate (Ca (NO)3)2) Solution of composition, deposition conditions: pH 3.5, deposited at 45 ℃ for 3h, the coating thickness being 3 μm.
The SEM image of the pure magnesium/DCPD coating is shown in fig. 2. Wherein Bi is 400 times, and Bii is 1000 times.
HA and DCPD coatings are formed by chemical bonding of calcium phosphate and magnesium matrices.
EXAMPLE 3 pure magnesium/DCPD + SA coating composite
a. The pure magnesium/DCPD coated composite material prepared in example 2 was treated with stearic acid to form a pure magnesium/DCPD + SA coated composite material, which was immersed in a 0.5mol/L ethanol solution of stearic acid for 1.5h, the DCPD + SA coating layer was dependent on hydrogen bonding and physical adsorption, and the DCPD + SA coating layer had a thickness of 4 μm. .
SEM images of pure magnesium/DCPD + SA coatings are shown in FIG. 3. Wherein Ci is 100 times and Cii is 1000 times.
Example 4 simulation of aqueous humor immersion experiment
The pure magnesium/coating composites prepared in examples 1-3 and uncoated pure magnesium samples were immersed in a balanced salt solution (BSS, Alcon, USA) to examine corrosion resistance, ion release, sample weight change and pH change. Four prepared samples were placed on a purpose-made PVC plastic holder and soaked in a solution containing 150ml of balanced salt (BSS), and each sample was weighed before testing. 4 sets of samples were placed in each case in a flask, which was then brought to 37 ℃ and 5% CO2Incubator (Shanghai department of health 101). Table 1 shows the composition of aqueous humor and simulated aqueous humor (BSS).
Table 1 composition of aqueous and simulated aqueous humor.
Composition (I) Aqueous humor Balanced salt solution (Alcon)
Na+(mmol/L) 163 156
K+(mmol/L) 2.3-3.9 10.1
Ca2+(mmol/L) 1.8 3.3
Mg2+(mmol/L) 1.1 1.5
Cl-(mmol/L) 132 129
pH 7.38 7.4
Osmotic pressure (mmHg) 304 305
(1) Scanning by an electron microscope: the electron micrographs after various coating immersion experiments are shown in fig. 4-6, where fig. 4 is a magnified image of a DCPD coating at 100x (a) and 1000x (b); FIG. 5 shows DCPD + SA coatings at 100x (C) and 500x (D) magnified images; fig. 6 shows the HA coating at 2000x magnification. The experiment shows that: after being soaked in balanced salt solution, the calcium phosphorus coating (DCPD) and the calcium phosphorus-stearic acid (DCPD + SA) coating have a small amount of cracks and are dissolved, and the surface of the Hydroxyapatite (HA) coating is complete. The coating technique was shown to have the effect of reducing the corrosion of pure magnesium in the aqueous humor, and reducing the degradation rate. The HA coating forms a mineral phase similar to bone and is smoother than the other two coatings, and the HA coating is more stable than DCPD or DCPD + SA.
(2) Changes in pH values of each group in balanced salt solution:
the pH value of each sample in the balanced salt solution changes as shown in FIG. 7, and hydroxide released by pure magnesium in the degradation process can raise the pH value of the solution, so the pH values of different samples are different, and the corrosion strength of the balanced salt solution to the samples is reflected.
Mg+2H2O→Mg2++2OH-+H2
As can be seen in fig. 7, the uncoated pure magnesium samples had significantly higher pH values than the respective pure magnesium/coating samples, indicating that the coating was effective in reducing corrosion of the balanced salt solution.
(3) Weight change of each group of samples in balanced salt solution
The weight change in the balanced salt solution for each set of samples is shown in fig. 8, and the weight decrease or increase in the degradation process for the pure magnesium/coating samples is related to the dissolution of the coating, the degradation of the matrix, and the hydrogen peroxide deposition.
As can be seen from fig. 8, the weight change of the pure magnesium group and the HA group is small, the weight loss of the DCPD and DCPD + SA groups in the second day after soaking is obvious, and the weight loss of the pure magnesium group is small, which indicates that the main reason for the weight loss of the sample in the early stage is the dissolution of the coating. The HA group coating is less soluble in the balanced salt solution and effectively protects the substrate from corrosion by the balanced salt solution, and later weight gain should be associated with hydrogen peroxide deposition.
(4) Ion concentration variation in balanced salt solution of each group of samples
The ion concentration changes in the balanced salt solutions of the samples of each group are shown in fig. 9-11, which respectively illustrate the changes of magnesium, calcium and phosphorus concentrations in the soaking test process, 2ml of different soaking solutions are respectively extracted on the 1 st, 5 th and 9 th days of soaking, and are diluted twice, and the contents of magnesium, calcium and phosphorus in the solutions are detected, and the data of the contents are obtained from the national magnesium alloy engineering research center of Chongqing university. The hydroxyapatite, calcium and phosphorus + stearic acid coating contains calcium ions and magnesium ions, and the dissolution of the coating and the degradation of the matrix release the magnesium, calcium and phosphorus ions in an immersion experiment. The level of ion concentration also reflects the ability of the coating to protect a pure magnesium substrate.
As can be seen from fig. 9: the magnesium ion concentration of each coating layer group is obviously reduced compared with that of a pure magnesium group, which shows that the coating effectively reduces the degradation of a pure magnesium matrix and the release of magnesium ions; fig. 10 and 11 show that the HA group is free from phosphate ion release and HAs a lower calcium ion concentration than the DCPD and DCPD + SA groups, indicating that the HA coating is effective in preventing dissolution of the coating by the balanced salt solution.
EXAMPLE 5 Effect of different coatings on the metabolic Activity and necrosis of HTCFs
Primary human eye Tenon's cystic fibroblasts (HTCFs) were cultured in 60mm culture dishes, the medium consisting of DMEM (Gbico, USA)) containing 10% fetal bovine serum (FBS, USA) and 1% penicillin/streptomycin (Gbico, USA)) was changed every 2-3 days, subculture was performed when the cells were 80% long, the cells were digested with 0.25% trypsin and 0.02% EDTA at 37 ℃ for 5 minutes, and the HTCFs cells were transferred to 25cm2The flask (BD Falcon, BD Biosciences, Broendby, Denmark) was further incubated at 37 ℃ with 5% CO2Subculture is carried out in an incubator. The samples prepared in examples 1-3 and the wafer samples prepared from pure titanium were immersed in 70% ethanol for 10 minutes and rinsed twice with distilled water, then dried under uv light and placed in 24-well plates (BD Falcon, BD Biosciences, Broendby, Denmark), 4 parallel samples each; subcultured HTCFs cells were reinoculated at 5 × 10 per well4And (4) respectively.
(1) Detection of metabolic activity of HTCFs by MTT method
The results are shown in fig. 12, with multiple curves representing the change in metabolic activity of HTCFs treated with different pure magnesium/coated composite samples from day 1 to day 7. The P-values of the different treatments are statistically significant (P)Treatment of<0.001). The metabolic activity of the DCPD + SA-coated samples decreased gradually from day 2 to day 7, significantly compared to the other group samples. The HTCFs seeded on pure titanium plates had the highest viability. The HA-coated group showed higher metabolic activity on day 2, but the viability decreased gradually and was lower than the DCPD sample group from day 4. No statistical significance was observed for the temporal P-value (P)time0.195), indicating that time has no significant effect on the metabolic activity of HTCFs.
(2) LDH method for detecting influence of pure magnesium of different coatings on HTCFs necrosis
The LDH assay was used to examine the cytotoxicity of HTCFs necrosis seeded on different samples, and the results are shown in fig. 13, with multiple curves representing the toxicity change of HTCFs treated with different pure magnesium/coated composite samples from day 1 to day 7. The P-values of the different treatments are statistically significant (P)Treatment of<0.001). The HA-coated sample group was the least cytotoxic and was statistically different from the other groups. The cytotoxicity of DCPD + SA group was higher than that of HA and DCPD group, and the p-value at time was not statistically significant (ptime=0.260)。
Example 6
(1) Anti-proliferation of Tenon's bursa fibroblasts by different coatings of pure magnesium
Proliferation of HTCF was monitored by incorporation of 5-bromo-2-deoxyuridine (BrdU) into cellular DNA using the cell proliferation BrdU assay kit (Merck KGaA, Darmstadt, germany). The procedure of example 5 was followed, and different coatings of pure magnesium were plated in 24-well plates and inoculated at 0.5X 104Individual cells/mL of HTCFs, 0.5mL per well. The cells were incubated in the incubator for 48 hours, then the cellular DNA was labeled with BrdU labeling reagent for 24 hours, and the cells were incubated with anti-BrdU antibody for 60 minutes at room temperature. The cells were then washed, peroxidase-labeled goat anti-mouse IgG was added and the cells were incubated for 30 minutes. After the final addition of substrate solution, the data were read using a spectrophotometer microplate reader with a dual wavelength setting at 450/595 nm. Meanwhile, titanium and glass sheets were used as controls, and 6 specimens were tested for each set of samples. Data were analyzed using one-way analysis of variance (SPSS 24). Wherein p is compared with glass<0.001;N=6。
The relative proliferation rates of different coatings of pure magnesium to HTCFs are shown in fig. 14, and it can be seen from fig. 14 that HTCF seeded on titanium sheets showed the most proliferation capacity, and the cell proliferation rate of titanium sheets was significantly higher than that of glass sheets (p ═ 0.049). The proliferation rate of the DCPD + SA coating group was significantly lower than that of the glass group (p ═ 0.047); the results for the DCPD group were almost identical to the glass group; the proliferation rate of the HA group was slightly higher than that of the DCPD group. In addition, compared with titanium sheets, the pure magnesium with the coating has lower proliferation rate and has the function of inhibiting the proliferation of HTCFs, so that the pure magnesium composite material with the coating has better superiority in preparing glaucoma drainage devices than the existing titanium material.
(2) Effect of different coating pure magnesium on fibroblast specific protein a-SMA expression
alpha-SMA protein is a myofibrillar marker that causes fibroblast proliferation and wound scarring, and the effect of different coatings of pure magnesium on fibroblast specific protein a-SMA expression is shown in fig. 15. As can be seen in fig. 15, the glass plate sets had the highest expression of α -SMA compared to endogenous GAPDH expression. The titanium plate group showed slightly lower alpha-SMA expression levels than the glass group. All types of coated pure magnesium have lower alpha-SMA expression level than titanium sheet group or glass sheet group, and the pure magnesium composite material with the coating can inhibit the expression of fibroblast specific protein a-SMA. Wherein the DCPD group and the DCPD + SA group have similar expression of alpha-SMA; the HA group showed the lowest expression level of α -SMA, significantly lower than the glass (p ═ 0.037) and titanium (0.001) groups. This shows that the coated pure magnesium composite material can be used to prepare glaucoma drainage device to reduce postoperative scar and inhibit fibroblast proliferation, and can be used as degradable biomaterial.
Finally, it is noted that the above-mentioned preferred embodiments illustrate rather than limit the invention, and that, although the invention has been described in detail with reference to the above-mentioned preferred embodiments, it will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the scope of the invention as defined by the appended claims.

Claims (6)

1. The application of the pure magnesium/coating composite material in the preparation of the glaucoma drainage device is characterized in that the coating is hydroxyapatite, calcium phosphate or calcium phosphate-stearic acid, and the thickness of the coating is 2-4 mu m.
2. Use according to claim 1, wherein the pure magnesium is 99.99% magnesium.
3. A method for preparing a pure magnesium/coating composite for use according to claim 1, comprising the steps of:
a. carrying out hot extrusion on pure magnesium, polishing the surface of the pure magnesium by using sand paper, then carrying out ultrasonic cleaning, and drying;
b. and then it is formed into a coating using electrodeposition and conversion coating methods.
4. The method of claim 3, wherein the hot extrusion process is: the extrusion temperature is 170-180 ℃, and the extrusion ratio is 20-25.
5. The method as claimed in claim 3, wherein the sand paper is 320-.
6. The production method according to claim 3, wherein the ultrasonic cleaning uses acetone or ethanol.
CN201810385486.3A 2018-04-26 2018-04-26 Application of pure magnesium/coating composite material and preparation method thereof Active CN108525023B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN201810385486.3A CN108525023B (en) 2018-04-26 2018-04-26 Application of pure magnesium/coating composite material and preparation method thereof

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN201810385486.3A CN108525023B (en) 2018-04-26 2018-04-26 Application of pure magnesium/coating composite material and preparation method thereof

Publications (2)

Publication Number Publication Date
CN108525023A CN108525023A (en) 2018-09-14
CN108525023B true CN108525023B (en) 2021-06-15

Family

ID=63479302

Family Applications (1)

Application Number Title Priority Date Filing Date
CN201810385486.3A Active CN108525023B (en) 2018-04-26 2018-04-26 Application of pure magnesium/coating composite material and preparation method thereof

Country Status (1)

Country Link
CN (1) CN108525023B (en)

Families Citing this family (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3893721A4 (en) * 2019-01-18 2022-10-12 Avisi Technologies, Inc. Method and device for treating eye disease
CN110934684B (en) * 2019-11-21 2021-03-30 浙江大学 Glaucoma drainage valve with anti-proliferative drug sustained-release coating grafted on surface and preparation method thereof

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004190126A (en) * 2002-12-10 2004-07-08 Tadamasa Fujimura Magnesium alloy sheet having excellent corrosion resistance
CN101254314A (en) * 2007-03-02 2008-09-03 北京奥精医药科技有限公司 Hydroxylapatite coating magnesium alloy medical inner implantation material and method of preparing the same
CN101643929A (en) * 2009-08-31 2010-02-10 郑州大学 Pulse electrodeposition preparation method of hydroxyapatite coating on surface of pure magnesium or magnesium alloy
CN102787339A (en) * 2012-07-30 2012-11-21 同济大学 Method for preparing magnesium alloy - calcium phosphorus coating composite material by electrochemical deposition

Family Cites Families (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2016019078A1 (en) * 2014-07-30 2016-02-04 Tufts University Three dimensional printing of bio-ink compositions

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2004190126A (en) * 2002-12-10 2004-07-08 Tadamasa Fujimura Magnesium alloy sheet having excellent corrosion resistance
CN101254314A (en) * 2007-03-02 2008-09-03 北京奥精医药科技有限公司 Hydroxylapatite coating magnesium alloy medical inner implantation material and method of preparing the same
CN101643929A (en) * 2009-08-31 2010-02-10 郑州大学 Pulse electrodeposition preparation method of hydroxyapatite coating on surface of pure magnesium or magnesium alloy
CN102787339A (en) * 2012-07-30 2012-11-21 同济大学 Method for preparing magnesium alloy - calcium phosphorus coating composite material by electrochemical deposition

Non-Patent Citations (2)

* Cited by examiner, † Cited by third party
Title
A feasibility study of using biodegradable magnesium alloy in glaucoma drainage device;Li X J等;《International Journal of Ophthalmology》;20180118;第11卷(第1期);第139页左栏第2段、第140页左栏第1段 *
Li X J等.A feasibility study of using biodegradable magnesium alloy in glaucoma drainage device.《International Journal of Ophthalmology》.2018,第11卷(第1期), *

Also Published As

Publication number Publication date
CN108525023A (en) 2018-09-14

Similar Documents

Publication Publication Date Title
Zhang et al. The dual function of Cu-doped TiO 2 coatings on titanium for application in percutaneous implants
Briggs et al. Formation of highly adherent nano-porous alumina on Ti-based substrates: a novel bone implant coating
Smetana Jr et al. The influence of hydrogel functional groups on cell behavior
Biazar et al. The healing effect of stem cells loaded in nanofibrous scaffolds on full thickness skin defects
CN108525023B (en) Application of pure magnesium/coating composite material and preparation method thereof
Huo et al. In vitro corrosion behavior and biocompatibility of nanostructured Ti6Al4V
Yang et al. Polydopamine-mediated long-term elution of the direct thrombin inhibitor bivalirudin from TiO 2 nanotubes for improved vascular biocompatibility
WO2008051228A1 (en) Skin substitutes, preparation methods and uses thereof
Lai Interrelationship between cross-linking structure, molecular stability, and cytocompatibility of amniotic membranes cross-linked with glutaraldehyde of varying concentrations
CN106606801B (en) A kind of Zn-ZnO system kirsite and the preparation method and application thereof
CN108478298B (en) Implant with polysaccharide coating capable of combining growth factors and preparation method thereof
Zhou et al. The fabrication and evaluation of a potential biomaterial produced with stem cell sheet technology for future regenerative medicine
Kartikasari et al. Titanium surface with nanospikes tunes macrophage polarization to produce inhibitory factors for osteoclastogenesis through nanotopographic cues
CN113529158B (en) Process for preparing porous structure on surface of TC4 titanium alloy by electrochemical dealloying method
Muzio et al. Polypropylene prostheses coated with silver nanoclusters/silica coating obtained by sputtering: Biocompatibility and antibacterial properties
Pham-Nguyen et al. Self-assembled cell sheets composed of mesenchymal stem cells and gelatin nanofibers for the treatment of full-thickness wounds
CN113106295A (en) Degradable biomedical material Zn-Si-X series zinc alloy and preparation method thereof
CN102302800B (en) Chitosan biofilm polypropylene mesh and preparation method thereof
Tajima et al. Alginate oligosaccharides modulate cell morphology, cell proliferation and collagen expression in human skin fibroblasts in vitro
AU2020104227A4 (en) Zinc-Calcium alloy series and preparation method and application thereof
CN106606806B (en) A kind of Zn-Mg1Ca system kirsite and the preparation method and application thereof
CN113174592B (en) Preparation and application of coating for improving biocompatibility of medical zinc/zinc alloy surface
CN101549172B (en) Hydroxylapatite-bioglass film and preparation technology thereof
CN110882424B (en) Oral cavity guided bone regeneration barrier membrane
CN103147111B (en) A kind of pure titanium differential arc oxidation coating and application thereof

Legal Events

Date Code Title Description
PB01 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant