CN106902391A - A kind of magnesium alloy is implanted into composite material and its preparation and application - Google Patents

A kind of magnesium alloy is implanted into composite material and its preparation and application Download PDF

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CN106902391A
CN106902391A CN201611262987.XA CN201611262987A CN106902391A CN 106902391 A CN106902391 A CN 106902391A CN 201611262987 A CN201611262987 A CN 201611262987A CN 106902391 A CN106902391 A CN 106902391A
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magnesium alloy
implant
arc oxidation
layer
abutment
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金杰
郑大才
段和洁
朱峥栩
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Zhejiang University of Technology ZJUT
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    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/02Inorganic materials
    • A61L27/04Metals or alloys
    • A61L27/047Other specific metals or alloys not covered by A61L27/042 - A61L27/045 or A61L27/06
    • AHUMAN NECESSITIES
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    • 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
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    • 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/50Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/56Porous materials, e.g. foams or sponges
    • CCHEMISTRY; METALLURGY
    • C25ELECTROLYTIC OR ELECTROPHORETIC PROCESSES; APPARATUS THEREFOR
    • C25DPROCESSES FOR THE ELECTROLYTIC OR ELECTROPHORETIC PRODUCTION OF COATINGS; ELECTROFORMING; APPARATUS THEREFOR
    • C25D11/00Electrolytic coating by surface reaction, i.e. forming conversion layers
    • C25D11/02Anodisation
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    • C25DPROCESSES FOR THE ELECTROLYTIC OR ELECTROPHORETIC PRODUCTION OF COATINGS; ELECTROFORMING; APPARATUS THEREFOR
    • C25D9/00Electrolytic coating other than with metals
    • C25D9/04Electrolytic coating other than with metals with inorganic materials
    • C25D9/08Electrolytic coating other than with metals with inorganic materials by cathodic processes
    • C25D9/12Electrolytic coating other than with metals with inorganic materials by cathodic processes on light metals
    • GPHYSICS
    • G06COMPUTING; CALCULATING OR COUNTING
    • G06TIMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/002D [Two Dimensional] image generation
    • G06T11/003Reconstruction from projections, e.g. tomography
    • G06T11/008Specific post-processing after tomographic reconstruction, e.g. voxelisation, metal artifact correction
    • GPHYSICS
    • G06COMPUTING; CALCULATING OR COUNTING
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    • 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
    • A61L2300/40Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/412Tissue-regenerating or healing or proliferative agents
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    • A61L2430/00Materials or treatment for tissue regeneration
    • A61L2430/02Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants
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    • G06T2207/30004Biomedical image processing
    • G06T2207/30008Bone
    • GPHYSICS
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Abstract

The invention discloses a kind of magnesium alloy implantation composite material and its preparation and application, the magnesium alloy implantation composite material is magnesium alloy abutment of implant through the model that 3D printing makes with magnesium alloy powder, differential arc oxidation film layer is formed using micro-arc oxidation on magnesium alloy abutment of implant surface, then hydroxyapatite layer or fluorine hydroxyapatite layer are formed using electrochemical deposition method in micro-arc oxidation films layer surface again, finally forms polylactic acid layers in hydroxyapatite layer or fluorine hydroxyapatite layer surface impregnation;The present invention is from the data acquisition of original impaired bone structure to the preparation of final multicoat composite construction, realize the personalized exploitation of magnesium alloy implant material, obtain high-quality magnesium alloy implantation composite material, wherein polarization test shows that its corrosion resistance obtains 4 liftings of the order of magnitude, and there is the composite material of magnesium alloy after prepared by osteoblasts cultivation display more preferable osteocyte to promote ability.

Description

A kind of magnesium alloy is implanted into composite material and its preparation and application
(1) technical field
The present invention relates to a kind of magnesium alloy multi-layer biological composite with good biocompatibility and preparation method thereof, I.e. by carrying out the scanning of multi-layer spiral CT to the impaired bone structure of human body, initial data is then carried out into treatment reparation, then pass through Prepared by the methods such as 3D printing, differential arc oxidation, electrochemical deposition have magnesium alloy/differential arc oxidation film layer/hydroxyapatite (or fluorine hydroxyl Base apatite)/PLA boiomacromolecule Rotating fields implantation composite material.
(2) background technology
At present in clinical practice field, medical metal material mainly has stainless steel, cobalt-base alloys and titanium alloy etc. several big Class material, but there are some drawbacks in this few class material, and such as 316L stainless steels produce gap rotten sometimes after human body is implanted into The problems such as erosion, fretting corrosion and fatigue corrosion rupture.Titanium alloy and stainless steel material all have larger elastic mould value, Stress-shielding effect can be caused in human body, causes bone tissue to heal slow, graft failure can be caused when serious.Additionally, stainless steel Bio-inert material is with titanium-base alloy, it is necessary to operation taking-up again, increased pain and the doctor of patient after bone tissue reparation Treatment expense is born.It is heavier and magnesium and magnesium alloy materials are widely paid close attention to its good biodegradability properties and biocompatibility What is wanted is magnesium alloy close with the density and mechanical property of bone structure, can significantly avoid stress-shielding effect, improves implantation Success rate.
The method for preparing biological medical magnesium alloy at present mainly includes:Smelting process, powder metallurgy and fused salt electrolysis process.But pass System process has that technological operation degree-of-difficulty factor is big, power consumption is big in preparation process, high cost, automate it is low, from And limit its extensive utilization in medical field;Powder metallurgic method sintering time in preparation process is short, is oxidized easily, difficult To control setting rate and be difficult to obtain complex-shaped structure;The preparation process of discharge plasma sintering method it is relatively costly and Must carry out under vacuum conditions.And new laser gain material manufacturing technology (3D printing), not only the advantage with high precision and Real metallurgical binding can be reached in forming process, the shortcoming caused by magnesium alloy conventional fabrication processes is overcome.3D printing Technology be based on mathematical model, with powdery metal or plastic or other material, by way of successively melting and piling up come The technology of constructed object.Existing bioengineering field can carry out 3D printing in bone structure by multi-layer spiral CT three-dimensional rebuilding The structure of aspect, the three-dimensional reconstruction based on multi-layer spiral CT improves modality conversion between entity world and digital world by common Resolution ratio, can scan, edit and replication entity object, create accurate copy or optimization original paper.
The chemical property of magnesium is extremely active, cavernous oxide-film is easily generated in corrosive medium so that magnesium alloy Mechanical performance reduction, influences the performance of implant.Zeng R C etc.【Zeng R C,Wolfgang D,Frank W,et al.Progress and challenge formagnesium alloys as biomaterials[J] .Adv.Eng.Mater.,2008,10(8):B3】Magnesium and its alloy be have studied in various simulated body fluids (simulated body Fluid, SBF) in corrosive nature, its pH- potential diagram shows that magnesium alloy can occur Mg (s)+2H in aqueous2O(aq)→ H2(g)+Mg(OH)2S () is reacted and causes corrosion.Therefore, in order to improve the corrosion resistance of magnesium alloy, necessary surface is modified The corrosion resistance of magnesium alloy can be significantly improved.Differential arc oxidization technique (Micro-arc oxidation, MAO) be it is a kind of recently The process for modifying surface for growing up, the technology is that directly parent metal is become by micro-arc discharge area instantaneous high-temperature high-pressure sinter Into oxide ceramics, and obtain thicker oxidation film.The activation of medical alloy surface oxide film is current tooth-planting material A kind of most promising method in material surface active, can significantly improve stability of the magnesium alloy in human body.GUO Huixia Deng【GUO Hui-xia,MA Ying,WANG Jing-song,et al.Corrosion behavior of micro-arc oxidation coating onAZ91D magnesium alloy in NaCl solutions with different concentrations[J].Trans.Nonferrous Met.Soc.China 22(2012)1786-1793.】Have studied micro- The corrosion behavior of magnesium alloy AZ31 after arc oxidation processes in the NaCl solution of various concentrations, as a result shows, the corrosion of sample Speed increases with the rising of chlorine ion concentration, but more untreated magnesium alloy, and sample etches performance is all obtained after differential of the arc treatment To greatly being lifted.
Biomedical metallic material is poor in the presence of conductive, heat conductivility, contacts perishable with other metals, Metal ion release The problems such as.In order to solve these problems, hydroxyapatite (HA:Ca10(PO4)6(OH)2) because its have good synosteosis performance, Biocompatibility and widely paid close attention to.Hydroxyapatite has similar chemical composition and crystal structure with bone tissue, this Just there is larger adhesive force in a short time after planting material implantation organism, material/bone interface can be made to form strong bonded, have Beneficial to the initial maintenance of graft materials, can effectively suppress metal ion to the release in organism, hydroxyapatite may be used also in addition To extend the service life of implant.But hydroxyapatite is easy to fatigue failure, for load implant, hydroxyapatite coat Layer is even more and is easily come off from implant.Hydroxyapatite poor mechanical properties, its bending strength in itself is less than 100MPa.This The success rate that implant is implanted into vivo can be substantially reduced.And by and the combination of magnesium alloy surface micro-arc oxidation can significantly carry The binding ability of stability of the magnesium alloy high in human body, lifting hydroxyapatite layer and matrix.Current magnesium surface oxidation film Activation it is important that how to form the oxidation film of surface hydroxyl apatite, usual way has two kinds:One is magnesium alloy Surface active coating, i.e., processed by differential arc oxidation and directly generate the hydroxyapatite coat with bioactivity in Mg alloy surface Layer;Another is magnesium surface activation modification, i.e., after processing metal surface, the oxide layer of magnesium is formed in magnesium surface, then by material Material is placed in physiological environment or simulation physiological environment in the formation of its spatial induction HA.But both approaches are for preparing environment With requirement higher.The activation modification of magnesium surface needs to be carried out in the environment of HTHP and has to operating environment among these There is requirement higher, which has limited further applying for magnesium matrix hydroxyapatite coating layer.
The preparation of hydroxyapatite is carried out to the magnesium alloy substrate of differential arc oxidation pre-treatment using electrochemical deposition, more at present Common hydro-thermal method prepares hydroxyapatite and compares with hot spray process, and the method can significantly reduce preparation temperature, improves experiment Operability, is conducive to the popularization of magnesium alloy/hydroxyapatite composite.But the meeting in performance of simple electrodeposited coating There is caducous tendency, causing the service life of coating reduces.Therefore, it is further to improve electro-deposition hydroxyapatite coating layer Adhesion and composite biocompatibility, the hydroxyapatite layer to surface can carry out the system of boiomacromolecule coating It is standby.The present invention carries out three-dimensional reconstruction by original impaired bone structure multi-slice Spiral CT, is carried out using 3D printing technique The preparation of magnesium alloy materials, the differential arc oxidation for then carrying out surface to it is processed to improve the corrosion resistance of magnesium alloy substrate, and Prepared for prepared by ensuing coating.It is prepared by the electrochemical deposition that hydroxyapatite coating layer is carried out in electrochemical deposition liquid, And carry out boiomacromolecule layer film preparation, magnesium alloy multi-layer biological composite is realized by a series of PROCESS FOR TREATMENT Preparation, obtain matching high, high performance composite construction.And so far, this systemic, high reproducibility, high-compatibility The preparation of composite material of magnesium alloy have not been reported.
(3) content of the invention
It is an object of the present invention to provide a kind of magnesium alloy multi-layer biological composite with good biocompatibility and its system Preparation Method, based on multi-layer spiral CT three-dimensional rebuilding, carries out the 3D printing of magnesium alloy abutment of implant and magnesium alloy is implanted into Body matrix carries out a series of surface treatments such as differential arc oxidation, electrochemical deposition and boiomacromolecule layer preparation and prepares magnesium alloy plant Enter body matrix/differential arc oxidation film layer/hydroxyapatite (HAP) or fluorine hydroxyapatite (FHAP) layer/PLA boiomacromolecule The magnesium alloy implantation composite material of Rotating fields.The present invention solves magnesium alloy implant material poor corrosion resistance, degraded speed Degree is fast, and the low problem of Gegenbaur's cell dependency improves the decay resistance and bioactivity of magnesium alloy substrate, is that magnesium alloy is planted The further application for entering body material provides thinking.
The technical solution adopted by the present invention is:
The present invention provides a kind of magnesium alloy implantation composite material, and the magnesium alloy is implanted into composite material with magnesium alloy powder The model made through 3D printing is magnesium alloy abutment of implant, is formed using micro-arc oxidation on magnesium alloy abutment of implant surface Differential arc oxidation film layer (i.e. arc differential oxide ceramic layer), then forms hydroxyl in micro-arc oxidation films layer surface using electrochemical deposition method again Base apatite layer or fluorine hydroxyapatite layer, finally form poly- breast in hydroxyapatite layer or fluorine hydroxyapatite layer surface impregnation Acid layer (i.e. boiomacromolecule layer);Differential arc oxidation liquid composition is used by the micro-arc oxidation:8~12g/L Na2SiO3, 8~ 12g/L Na3PO4, 6~10g/L NaOH, 3~7g/L KF, 3~8g/L Na2CO3, 1~5g/L KOH, 50~100mL/L without Water-ethanol, solvent is deionized water, pH value nature;Electrochemical deposition liquid composition is used by the hydroxyapatite layer: 0.042mol/L Ca(NO3)2、0.5mol/L NaNO3、0.025mol/L NH4H2PO4, 30-50mL/L absolute ethyl alcohols, 30- 50mL/L hydrogen peroxide, 0.004-0.006mol/L APES OP-21,0.1-0.2mol/L trisodium citrates, it is molten Agent is deionized water, is 4.3-4.5 with trometamol and nitre acid for adjusting pH;The fluorine hydroxyapatite layer electrochemical deposition liquid is To addition concentration 0.0008mol/L NaF in electrochemical deposition liquid used by hydroxyapatite layer.
Further, preferably differential arc oxidation liquid composition is:10g/L Na2SiO3、10g/L Na3PO4、8g/L NaOH、5g/L KF、6g/L Na2CO3, 3g/L KOH, 75mL/L absolute ethyl alcohols, solvent is deionized water, pH value nature.It is preferred that electrochemical deposition Liquid is constituted:0.042mol/L Ca(NO3)2、0.5mol/L NaNO3、0.025mol/L NH4H2PO4, 40mL/L absolute ethyl alcohols, 40mL/L hydrogen peroxide, 0.005mol/L APES OP-21,0.15mol/L trisodium citrates, solvent is deionization Water, is 4.4 with trometamol and nitre acid for adjusting pH.The fluorine hydroxyapatite layer electrochemical deposition liquid is to hydroxyapatite layer Concentration 0.0008mol/L NaF are added in electrochemical deposition liquid used.
Further, preferably described differential arc oxidation film layer thickness is 20 μm~30 μm, the hydroxyapatite layer or fluorine hydroxyl Apatite layer thickness is 4 μm~6 μm.
Further, preferably described differential arc oxidation film layer is prepared as follows:It is with described magnesium alloy abutment of implant Anode, stainless steel is negative electrode, is 550~650Hz in frequency in differential arc oxidation liquid, and the differential of the arc time is 15~30min, duty Than being 15~30%, current density is 20A/cm2, operation temperature be room temperature (optimized frequency is 600Hz, differential of the arc time 20min, Dutycycle is 20%, and current density is 20A/cm2, 23 DEG C of operation temperature) under the conditions of carry out differential arc oxidation reaction, after reaction terminates Magnesium alloy abutment of implant is taken out, is cleaned by ultrasonic (preferably 15min) in deionized water, dried in 20-45 DEG C of baking oven, obtained The magnesium alloy abutment of implant that surface forms micro-arc oxidation films Rotating fields is obtained, magnesium alloy abutment of implant/micro-arc oxidation films are designated as Layer.
Further, preferably described hydroxyapatite layer or fluorine hydroxyapatite layer are prepared as follows:Formed with surface The magnesium alloy abutment of implant of differential arc oxidation film layer is working electrode, and, used as to electrode, saturated calomel electrode is used as reference for platinized platinum Electrode, in electrochemical deposition liquid, constant current mode, current density is 4-6mA/cm2(preferably 5mA/cm2), depositing temperature is 37 DEG C Under conditions of carry out electrochemical deposition 90-150min (preferably 120min) after, described magnesium alloy abutment of implant is taken out, use Deionized water is cleaned, and room temperature is dried;Immerse again in the NaOH aqueous solution of 1-2mol/L (preferably 2mol/L), 2- is soaked at 80 DEG C 4h (preferably 3h), is then cleaned repeatedly with deionized water, after room temperature is dried, in tube furnace under argon gas or vacuum protection atmosphere In carry out the high temperature anneal, be warming up to 200 DEG C with the speed of 10 DEG C/min, be incubated 2h, obtain surface shape successively from outside to inside Into hydroxyapatite layer or fluorine hydroxyapatite layer, the magnesium alloy abutment of implant of micro-arc oxidation films Rotating fields, magnesium alloy is designated as Abutment of implant/differential arc oxidation film layer/hydroxyapatite layer or fluorine hydroxyapatite layer.The system of the fluorine hydroxyapatite layer Standby is that electrochemical deposition liquid is changed to addition concentration 0.0008mol/L in electrochemical deposition liquid used by hydroxyapatite layer NaF, other operations are identical.
Further, the thickness of preferably described polylactic acid layers is 5 μm~10 μm.
Further, preferably described polylactic acid layers are prepared as follows:Polylactic acid powder is added in dichloromethane, room Warm uniform stirring 6 hours, obtains the PLA solution of mass concentration 2.5%;The PLA is 2.5 with dichloromethane mass ratio: 97.5;Surface is sequentially formed hydroxyapatite layer or fluorine hydroxyapatite layer, the magnesium alloy of differential arc oxidation film layer from outside to inside In abutment of implant immersion PLA solution, after soaking at room temperature 20-30s, proposed with the constant speed of 15-25mm/min, logical Room temperature is dried in wind kitchen, and then deionized water is cleaned, and room temperature is dried, that is, obtain and sequentially form from outside to inside polylactic acid layers, hydroxyl Apatite layer or fluorine hydroxyapatite layer, the magnesium alloy implantation composite material of micro-arc oxidation films Rotating fields, are designated as magnesium alloy plant Enter body matrix/differential arc oxidation film layer/hydroxyapatite layer or fluorine hydroxyapatite layer/polylactic acid layers.
Further, preferably described magnesium alloy abutment of implant is prepared as follows:(1) impaired bone structure is carried out into CT to sweep Retouch, obtain the CT scan data of impaired bone structure, and be input to Materialise 3 d modeling softwares, carry out threshold value division, so The noise for importing image is removed using region growth method afterwards, removal, the segmentation both injured bones structural region of redundant data is carried out;(2) Segmentation is felt better behind damage bone structure region, further obtains impaired bone structure by Materialise 3 d modeling softwares opening operation Three-dimensional structure data, realization initial data is switched into three-dimensional structure data, then will obtain three-dimensional structure data input UG Software, obtains digitlization Cranial defect threedimensional model;(3) according to digitlization Cranial defect threedimensional model, design bone using CAD software and lack Module is damaged, STL models are obtained;(4) by STL mode input 3D printing equipment, then by magnesium alloy powder in ball mill (XQM-0.4L Planetary ball mill) in be well mixed, mill rotating speed be 250r/min, Ball-milling Time is 30min, employ nitrogen as be protect gas Body, obtains the magnesium alloy powder after ball milling (preferable particle size is 40 μm~50 μm);3D is added to beat the magnesium alloy powder after ball milling Printing apparatus, are molded using laser 3D printing, and the power of laser is 100~200W (preferably 150W), sweep speed 20m/min, arteries and veins 1~3ms wide, frequency 0.0Hz, 2~3mm of defocusing amount, spot diameter 0.2mm, print, individual layer under argon gas or vacuum protection atmosphere Print thickness 0.04mm, is printed according to STL models, obtains embryo material;The embryo material of acquisition is placed in electrochemical workstation (IviumStat) in the electrolytic cell equipped with agitating device, polishing fluid is volume ratio 1 in electrolytic cell:1:20 perchloric acid, glycerine and The mixed liquor of glacial acetic acid, in 30V constant voltage modes, liquid feeding nitrogen is cooled to -5 DEG C, and 100~200r/min of low whipping speed is (preferably Carry out electrochemical polish operation under conditions of 150r/min), obtain the embryo material after electrochemical polish, then successively with absolute alcohol, Acetone and deionized water are cleaned by ultrasonic, and dry at room temperature, obtain described magnesium alloy abutment of implant.
Further, preferably described magnesium alloy powder is AZ91D magnesium alloy powders, and particle diameter is 120 μm~150 μm.
The present invention also provides the preparation method that a kind of magnesium alloy is implanted into composite material, and methods described is:(1) will receive Damaging bone structure carries out CT scan, obtains the CT scan data of impaired bone structure, and it is soft to be input to Materialise three-dimensional modelings Part, carries out threshold value division, and the noise for importing image is then removed using region growth method, carries out removal, the segmentation of redundant data Both injured bones structural region;(2) after damage bone structure region is felt better in segmentation, further opened by Materialise 3 d modeling softwares Computing obtains the three-dimensional structure data of impaired bone structure, and initial data is switched to three-dimensional structure data by realization, then by acquisition Three-dimensional structure data is input into UG softwares, obtains digitlization Cranial defect threedimensional model;(3) according to digitlization Cranial defect threedimensional model, Cranial defect module is designed using CAD software, STL models are obtained;(4) by magnesium alloy powder, in ball mill, (XQM-0.4L is planetary Ball mill) in be well mixed, mill rotating speed be 250r/min, Ball-milling Time is 30min, and it is protective gas to employ nitrogen as, Obtain the magnesium alloy powder after ball milling (preferable particle size is 40 μm~50 μm);By STL mode input 3D printer equipment, then by ball Magnesium alloy powder after mill is placed in 3D printer equipment, is molded using laser 3D printing, and the power of laser is 100~200W (preferably 150W), sweep speed 20m/min, 1~3ms of pulsewidth, frequency 0.0Hz, 2~3mm of defocusing amount, spot diameter 0.2mm, argon Printed under gas or vacuum protection atmosphere, individual layer print thickness 0.04mm is printed according to STL models, obtain embryo material;To obtain The embryo material for obtaining is placed in electrolytic cell of the electrochemical workstation (IviumStat) equipped with agitating device, and polishing fluid is body in electrolytic cell Product compares 1:1:The mixed liquor of 20 perchloric acid, glycerine and glacial acetic acid, in 30V constant voltage modes, liquid feeding nitrogen is cooled to -5 DEG C, in stirring Electrochemical polish operation is carried out under conditions of 100~200r/min of speed (preferably 150r/min), after obtaining electrochemical polish Embryo material, then dried at room temperature with the ultrasonic cleaning of absolute alcohol, acetone and deionized water successively, obtain described magnesium alloy implantation Body matrix;(5) with described magnesium alloy abutment of implant as anode, stainless steel is negative electrode, in differential arc oxidation liquid, is in frequency 550~650Hz, the differential of the arc time is 15~30min, and dutycycle is 15~30%, and current density is 20A/cm2, operation temperature is (optimized frequency is 600Hz, differential of the arc time 20min to room temperature, and dutycycle is 20%, and current density is 20A/cm2, operation temperature 23 DEG C) under the conditions of carry out differential arc oxidation reaction, described magnesium alloy abutment of implant is taken out in reaction after terminating, surpass in deionized water Sound cleans (preferably 15min), is dried in 20-45 DEG C of baking oven, obtains the magnesium alloy that surface forms micro-arc oxidation films Rotating fields Abutment of implant, is designated as magnesium alloy abutment of implant/differential arc oxidation film layer;(6) the magnesium alloy implant base prepared with step (5) Body/differential arc oxidation film layer is working electrode, and platinized platinum is used as to electrode, and saturated calomel electrode is heavy in electrochemistry as reference electrode In hydrops, constant current mode, current density is 4-6mA/cm2(preferably 5mA/cm2), depositing temperature be 37 DEG C under conditions of carry out electricity After chemical deposition 90-150min (preferably 120min), described magnesium alloy abutment of implant/differential arc oxidation film layer is taken out, used Deionized water is cleaned, and room temperature is dried;Immerse again in the NaOH aqueous solution of 1-2mol/L (preferably 2mol/L), 2- is soaked at 80 DEG C 4h (preferably 3h), is then cleaned repeatedly with deionized water, after room temperature is dried, in tube furnace under argon gas or vacuum protection atmosphere In carry out the high temperature anneal, be warming up to 200 DEG C with the speed of 10 DEG C/min, be incubated 2h, obtain surface shape successively from outside to inside Into hydroxyapatite layer or fluorine hydroxyapatite layer, the magnesium alloy abutment of implant of micro-arc oxidation films Rotating fields, magnesium alloy is designated as Abutment of implant/differential arc oxidation film layer/hydroxyapatite layer or fluorine hydroxyapatite layer;(7) polylactic acid powder is added to two In chloromethanes, room temperature uniform stirring 6 hours obtains the PLA solution of mass concentration 2.5%;Magnesium alloy prepared by step (6) In abutment of implant/differential arc oxidation film layer/hydroxyapatite layer or fluorine hydroxyapatite layer immersion PLA solution, soaking at room temperature After 20-30s, propose that room temperature is dried in ventilating kitchen with the constant speed of 15-25mm/min, then deionized water is cleaned, room temperature Dry, that is, obtain and sequentially form from outside to inside polylactic acid layers, hydroxyapatite layer or fluorine hydroxyapatite layer, differential arc oxidation film layer The magnesium alloy implantation composite material of structure, is designated as magnesium alloy substrate/differential arc oxidation film layer/hydroxyapatite layer or fluorine hydroxyl Apatite layer/polylactic acid layers.
Additionally, the present invention also provides a kind of magnesium alloy implantation composite material answering in bone renovating material is prepared With.
Room temperature of the present invention refers to 25-30 DEG C.Differential arc oxidation film layer, hydroxyapatite layer or fluorine hydroxy-apatite in the present invention Rock layers control the thickness of thickness, polylactic acid layers to be controlled by impregnating repeatedly, lifting by controlling the reaction time.
Compared with the existing technology for preparing magnesium alloy implant, the beneficial effects are mainly as follows:
(1) present invention is solved using the 3D printing technique based on multi-layer spiral CT three-dimensional rebuilding in the preparation of matrix Complex process caused by the preparation methods such as conventional cast, sintering, oxidizable, the low problem of implant recovery accuracy, improves The structure precision and biocompatibility of magnesium alloy implant;
(2) present invention prepares bio-ceramic coating and can in the coating introduce calcium using differential arc oxidization technique in Mg alloy surface Deng the element favourable to bone growth, obtaining special micrometer level porous hole can strengthen the machinery knot of histocyte and implant Conjunction ability, and excellent binding ability can meet magnesium alloy implant clinical manipulation wearability demand and film layer it is long-acting Property;
(2) Mg alloy surface using electrochemical deposition technique after differential arc oxidation treatment prepares hydroxyapatite coating layer The methods such as the more traditional plasma spraying of method have low-temperature operation, and process is simple can be in complex-shaped and porous surface base The advantage of uniform coating is prepared on bottom, while the introducing of hydroxyapatite coating layer enhances the hydrophily of film surface, is conducive to Albumen significantly improves the migration of cell and increases in the absorption on surface, the Integrated implant of material is improved, so as to be conducive to bone tissue Healing;
(3) present invention carries out surface macromolecule layer using Best-Effort request machine to the magnesium alloy implant after electrodeposition process Prepare, improve coating corrosion resistance in vivo, further promote the reparation of bone tissue.
The present invention realizes magnesium conjunction from the data acquisition of original impaired bone structure to the preparation of final multicoat composite construction The personalized exploitation of golden implant material, obtains high-quality magnesium alloy implantation composite material, wherein polarization test display Its corrosion resistance obtains 4 liftings of the order of magnitude, and the composite material of magnesium alloy after prepared by osteoblasts cultivation display has more Good osteocyte promotes ability.
(4) illustrate
Fig. 1 is magnesium alloy abutment of implant/differential arc oxidation film layer/hydroxyapatite layer of the present invention (or fluorine hydroxy-apatite Stone)/polylactic acid layers composite structural representation;
Fig. 2 is the scanning electron microscope (SEM) photograph of the magnesium alloy matrix surface after differential arc oxidation in embodiment 1, and wherein a is to amplify 2000 After times, after b is to amplify 5000 times;
Fig. 3 is the EDS energy spectrum diagrams that magnesium alloy substrate carries out surface after differential arc oxidation and electrochemical deposition in embodiment 1;
Fig. 4 is the scanning electron microscope (SEM) photograph of the magnesium alloy matrix surface after differential arc oxidation and electrochemical deposition in embodiment 2, its After middle figure a is to amplify 1000 times, after b is to amplify 10000 times.
(5) specific embodiment
With reference to specific embodiment, the present invention is described further, but protection scope of the present invention is not limited in This:
In following examples, magnesium alloy implantation composite material has sandwich construction (such as Fig. 1), including arc differential oxide ceramic Layer, hydroxyapatite (or fluorine hydroxyapatite) layer and PLA boiomacromolecule layer.
Embodiment 1
1st, the preparation of magnesium alloy abutment of implant
(1) patient's bone structure is carried out into CT scan (slices spiral CTs of GE LightSpeed 16), carries out both injured bones structure number According to collection, data save as DICOM format;
(2) CT scan data of acquisition is input to Materialise 3 d modeling softwares (Materialise Magics20), threshold value division is carried out, the noise for importing image is then removed using region growth method, carry out going for redundant data Except, segmentation both injured bones structural region;
(3) three-dimensional structure data of impaired bone structure is obtained by Materialise 3 d modeling softwares opening operation, then The three-dimensional data that will be obtained is input into UG softwares (NX9.0) and obtains digitlization Cranial defect threedimensional model, and the reparation for carrying out Cranial defect sets Meter;
(4) being designed according to Cranial defect and the limbs line of force using CASE(Computer Aided Software Engineering) (CAD) (AutoCAD2010) carries out bone The design of defect module, obtains high-quality digital model.
(5) the digital model data that will be obtained are with the object STL mode inputs of standard to 3D printer (Focus- MD300 pulse lasers) in, AZ91D magnesium alloy powders (120 μm~150 μm of particle diameter) are well mixed in mixed powder machine, Mill rotating speed is 250r/min, and Ball-milling Time is 30min, and it is protective gas to employ nitrogen as, and obtains the magnesium alloy after ball milling Powder, particle diameter is 40 μm~50 μm.Magnesium alloy powder after ball milling is added into 3D printer, is molded using laser 3D printing, swashed The power of light is 200W, sweep speed 20m/min, pulsewidth 2ms, frequency 0.0Hz, defocusing amount 2.5mm, spot diameter 0.2mm, argon Printed under gas or vacuum protection atmosphere, individual layer print thickness 0.04mm, the embryo material of acquisition carries out electrochemical polish, and polishing fluid is Volume ratio 1:The mixed liquor of 9 perchloric acid, positive absolute ethyl alcohol, using electrochemical workstation (IviumStat) and be provided with stirring dress The electrolytic cell put is in constant current mode, current density 3A/dm2, -5 degrees Celsius of temperature (plus liquid nitrogen cooling), mixing speed 150r/min Under conditions of be polished operation, obtain embryo material of the surface roughness at 70 μm or so;Absolute alcohol, acetone is respectively adopted, goes Ionized water each ultrasonic cleaning of 15 minutes, carries out the de-oiling degreasing on embryo material surface, dries at room temperature, after obtaining electrochemical polish Magnesium alloy abutment of implant.
(6) with the dried magnesium alloy abutment of implant of step (5) as anode, stainless steel is negative electrode, in differential arc oxidation liquid In, it is 600Hz, differential of the arc time 20min in frequency, dutycycle is 20%, and current density is 20A/cm2, operation temperature is 23 DEG C Under the conditions of carry out differential arc oxidation treatment, magnesium alloy abutment of implant surface formed 20 μm of differential arc oxidation film layers, take out, go from It is cleaned by ultrasonic 15min in sub- water, is dried in 45 DEG C of baking oven, obtains surface and form 20 μm of magnesium conjunctions of micro-arc oxidation films Rotating fields Golden abutment of implant, is designated as magnesium alloy abutment of implant/differential arc oxidation film layer.Differential arc oxidation liquid is constituted:10g/L Na2SiO3、 10g/L Na3PO4、8g/L NaOH、5g/L KF、6g/L Na2CO3, 3g/L KOH, 75mL/L absolute ethyl alcohols, solvent for go from Sub- water, pH value nature.
(7) electro-deposition is carried out under three-electrode system.It is with step (6) magnesium alloy abutment of implant/differential arc oxidation film layer Working electrode, used as to electrode, used as reference electrode, in electrochemical deposition liquid, constant current mode is electric for saturated calomel electrode for platinized platinum Current density is 5mA/cm2, after depositing temperature under conditions of 37 DEG C to carry out electrochemical deposition 120min, by magnesium alloy implant base Body is taken out, and is washed with deionized water only, and room temperature is dried;Immerse again in the NaOH aqueous solution of 2mol/L, 3h is soaked at 80 DEG C, by phosphorus Acid calcium salt is fully converted to hydroxyapatite, is then cleaned repeatedly with deionized water, after room temperature is dried, is protected in argon gas or vacuum The high temperature anneal is carried out under shield atmosphere, the adhesion of hydroxyapatite layer and differential arc oxidation layer is improved, annealing temperature is 200 DEG C, 2h is incubated, wherein diamond heating speed is 10 DEG C/min, obtains magnesium alloy abutment of implant surface shape successively from the inside to the outside Into 20 μm of differential arc oxidation film layers, 5 μm of structures of hydroxyapatite (HAP) layer are designated as magnesium alloy abutment of implant/micro-arc oxidation films Layer/hydroxyapatite layer, scanning electron microscope (SEM) photograph is as shown in Figure 2;Electrochemical deposition liquid is constituted:0.042mol/L Ca(NO3)2、 0.5mol/L NaNO3、0.025mol/L NH4H2PO4, 40mL/L absolute ethyl alcohols, 40mL/L hydrogen peroxide, 0.005mol/L alkyl Phenol polyethenoxy ether OP-21,0.15mol/L trisodium citrate, solvent is deionized water, is with trometamol and nitre acid for adjusting pH 4.4。
(8) PLA powder (weight average molecular weight 150,000) is added to dichloromethane (DCM:Dichloromethane in), room Warm uniform stirring 6 hours, it is 2.5 that both add mass ratio:97.5, the PLA solution of 2.5wt.% is obtained, it is then immersed in step (7) magnesium alloy abutment of implant/differential arc oxidation film layer/hydroxyapatite layer, after soaking at room temperature 25s, in Best-Effort request machine (Shanghai Three grind science and technology produces SYDC-100 type Best-Effort requests coating machine) in the presence of, proposed with the constant speed of 20mm/min, in ventilation Room temperature is dried in kitchen.Then deionized water is cleaned, and room temperature is dried, you can obtain magnesium alloy abutment of implant surface from the inside to the outside according to 25 μm of differential arc oxidation film layers of secondary formation, 5 μm of hydroxyapatite layers, 8 μm of structures of polylactic acid layers are designated as magnesium alloy implant base The magnesium alloy implantation composite material of body/differential arc oxidation film layer/hydroxyapatite layer/polylactic acid layers structure, structural representation is shown in Shown in Fig. 1, EDS energy spectrum diagrams are as shown in Figure 3.
From figure 2 it can be seen that hydroxyapatite product is in bar sheet (a in Fig. 2), further amplify it can be seen that (Fig. 2 There is certain interval between middle b) hydroxyapatite, and differential of the arc hole is completely covered, coating uniform has cause, and this is conducive to surface biological The preparation of macromolecule layer, while also further enhancing the biocompatibility of magnesium alloy implant.
As seen from Figure 3, calcium phosphorus atoms ratio reaches 2.39, and more than theoretical value 1.67, this is due to deposition process and heat During treatment caused by the loss of phosphorus.
2nd, the performance test of magnesium alloy abutment of implant
(1) the dynamic polarization test of electrochemistry
By the present embodiment obtain magnesium alloy abutment of implant composite Hank solution (component be 8g/L NaCl, 0.4g/L KCl, 0.25g/L NaH2PO4·H2O, 0.35g/L NaHCO3, 0.06g/L Na2HPO4·2H2O, 0.19g/L MgCl2, 0.19g/L CaCl2·2H2O, 0.06g/L MgSO4·7H2O and 1g/L glucose, deionized water is prepared, pH 7.8) In carry out the dynamic polarization test of electrochemistry, it is electrochemical workstation (IviumStat) to use equipment, and its specific test parameter is:Sweep Speed is retouched for 1mVs-1, sweep limits is -2.0V to 1.0V, magnesium alloy implantation composite material (AZ91D/ obtained in step 1 MAO/HAP/PLA) as working electrode, platinum electrode make to electrode, saturated calomel electrode as reference electrode, at a temperature of 37 DEG C Tested, be control, the experimental data for measuring such as table 1 below with the magnesium alloy abutment of implant (magnesium alloy AZ31) of step (5) It is shown:
The analysis result of polarization curve in table 1.Hank solution
Sample Ecorr(V)
Magnesium alloy AZ31 -1.73
AZ91D/MAO/HAP/PLA -1.22
Can be obtained by table 1, the corrosion potential of magnesium alloy implantation composite material prepared by present case is from being not handled by - 1.22V is arrived in preceding -1.73V liftings.In general, a corrosion potential higher shows that it has more preferable decay resistance, Therefore, the magnesium alloy implantation composite material that prepared by present case has been obviously improved the decay resistance of magnesium alloy substrate.From corrosion Current density can be seen that the corrosion electric current density of the matrix after treatment reduces 4 orders of magnitude, and this shows prepared by present case Magnesium alloy composite coating material significantly reduces the corrosion rate of magnesium alloy substrate.Dynamic polarization test results can be illustrated, made Standby magnesium alloy composite coating material can effectively improve the decay resistance of magnesium alloy substrate.
(2) attachment Gegenbaur's cell experiment
The magnesium alloy implantation composite material obtained to step 1 carries out cell culture experiments:To be obtained from adult rabbits body Gegenbaur's cell cleaned twice with pH=7.5 phosphate buffers, be then collected by centrifugation, take cell precipitation be seeded to DMEM training In nutrient solution, in 5%CO2, to be cultivated 1 week at 37 DEG C, the cell of acquisition is configured to 5 × 10 with pH=7.5 phosphate buffers5/ ml cells Suspension.
Magnesium alloy implantation prepared by magnesium alloy abutment of implant (magnesium alloy AZ31) and step (8) prepared by step (5) Composite material (AZ91D/MAO/HAP/PLA) is sterilized 40 minutes in 110 DEG C of water vapours respectively, and 5mm × 5mm is then taken respectively The sample of × 1mm sizes is added in six orifice plates, then is separately added into 5 × 105/ ml Gegenbaur's cell suspension 1ml, add 10ml and contain The DMEM nutrient solutions of 10% hyclone (FBS), 5%CO2, 37 DEG C are cultivated 24h, are washed with pH=7.5 phosphate buffer solutions afterwards Three removal non-adhering cells of plate, are subsequently adding 0.5ml digestive juices (pancreas enzyme -EDTA) digestion, and the standard for adding 0.5ml disappears Change liquid (pancreatin inhibitor) and terminate digestion, be made cell suspension, cell count is carried out with Z2 type cellular granularity calculating instruments.It is counted Result is as shown in table 2 below:
The cell count of each group after the culture in 24 hours of 2. Gegenbaur's cell of table
Sample Attached cell number
Magnesium alloy AZ31 62000±2000
AZ91D/MAO/HAP/PLA 71000±2000
The Ti/MAO/HAP/PLC composite coating materials as obtained in table 2 can obtain present case have more attachment skeletonization thin Born of the same parents, this Ti/MAO/HAP/PLC composite coating material for showing to prepare has preferably promotion bone cell growth ability, effectively Improve the bioactivity of magnesium alloy substrate material.
Embodiment 2
Step (1)~(5) are identical with the condition in embodiment 1;
Be changed to for differential arc oxidation treatment fluid composition in the step of embodiment 1 (6) by step (6):8g/L Na2SiO3、10g/L Na3PO4、8g/L NaOH、3g/L KF、3g/L Na2CO3, 1g/L KOH, 50mL/L absolute ethyl alcohols, solvent is deionized water, pH Value nature.The control parameter of differential arc oxidation is changed to:Frequency is 550Hz, and the differential of the arc time is 15min, and dutycycle is 15%, and electric current is close It is 15A/cm to spend2, remaining condition is constant;Obtain magnesium alloy abutment of implant/differential arc oxidation film layer.
Be changed to for electrochemical deposition liquid composition in the step of embodiment 1 (7) by step (7):0.042mol/L Ca(NO3)2、 0.5mol/L NaNO3、0.025mol/L NH4H2PO4, 30mL/L absolute ethyl alcohols, 30mL/L hydrogen peroxide, 0.004mol/L alkyl In phenol polyethenoxy ether OP-21,0.1mol/L trisodium citrate, the deposition liquid of 0.0008mol/L NaF, solvent is deionization Water, is 4.3 with trometamol and nitre acid for adjusting pH.Electrochemical deposition condition is changed to:Constant current mode, current density is 4mA/cm2, Depositing temperature is 37 DEG C, and sedimentation time is 90min.The concentration of NaOH is changed to 1mol/L, and soak time is changed to 2h, and remaining condition is not Become, remaining condition is constant;ESEM is as shown in Figure 4.Obtain magnesium alloy abutment of implant/differential arc oxidation film layer/hydroxy-apatite Rock layers.SEM photograph is shown in Fig. 4,.
(soak time in the step of embodiment 1 (8) is changed to 20s to step by 8, and lifting speed is changed to the perseverance of 15mm/min Constant speed degree, remaining condition is constant.Magnesium alloy implantation composite material is obtained ,/differential arc oxidation film layer thickness is 20 μm, hydroxy-apatite Rock layers thickness is 4 μm, and polylactic acid layers thickness is 5 μm.
Fig. 4 is that the present embodiment gained magnesium alloy substrate carries out the SEM after differential arc oxidation and electrochemical fluorine hydroxyapatite Photo, it can be seen that fluorine hydroxyapatite product prepared by electro-deposition is in nanoscale acicular texture, can be seen after amplification Obvious flower-like structure, this is, because differential arc oxidation hole increases surface area, to promote the nucleation rate of matrix surface, is caused One lower crystallite dimension, and low crystallite dimension is more beneficial for improving the bioactivity of material, enhances magnesium alloy Biocompatibility.Meanwhile, it can clearly be seen that differential arc oxidation hole is covered very well after deposit, obtain covering uniform table Face.
Embodiment 3
Step (1)~(5) are identical with the condition in embodiment 1;
Be changed to for differential arc oxidation treatment fluid composition in the step of embodiment 1 (6) by step (6):12g/L Na2SiO3、12g/ L Na3PO4、10g/L NaOH、7g/L KF、8g/L Na2CO3, 5g/L KOH, 100mL/L absolute ethyl alcohols, solvent is deionization Water, pH value nature.The control parameter of differential arc oxidation is changed to:Frequency is 650Hz, and the differential of the arc time is 30min, and dutycycle is 30%, Current density is 20A/cm2, remaining condition is constant;Obtain magnesium alloy abutment of implant/differential arc oxidation film layer.
Be changed to for electrochemical deposition liquid composition in the step of embodiment 1 (7) by step (7):0.042mol/L Ca(NO3)2、 0.5mol/L NaNO3、0.025mol/L NH4H2PO4, 50mL/L absolute ethyl alcohols, 50mL/L hydrogen peroxide, 0.006mol/L alkyl In phenol polyethenoxy ether OP-21,0.2mol/L trisodium citrate, the deposition liquid of 0.0008mol/L NaF, solvent is deionization Water, is 4.5 with trometamol and nitre acid for adjusting pH, and electrochemical deposition condition is changed to:Constant current mode, current density is 6mA/cm2, Depositing temperature is 37 DEG C, and sedimentation time is 150min.The concentration of NaOH is changed to 2mol/L, and soak time is changed to 4h, remaining condition Constant, remaining condition is constant;Obtain magnesium alloy abutment of implant/differential arc oxidation film layer/hydroxyapatite layer.
Soak time in the step of embodiment 1 (8) is changed to 30s by step (8), and lifting speed is changed to the perseverance of 25mm/min Constant speed degree, remaining condition is constant.Magnesium alloy implantation composite material is obtained, differential arc oxidation film layer thickness is 30 μm, hydroxy-apatite Rock layers thickness is 6 μm, and polylactic acid layers thickness is 10 μm.

Claims (10)

1. a kind of magnesium alloy is implanted into composite material, it is characterised in that the magnesium alloy implantation composite material is passed through with magnesium alloy powder The model that 3D printing makes is magnesium alloy abutment of implant, forms micro- using micro-arc oxidation on magnesium alloy abutment of implant surface Arc oxidation film layer, then forms hydroxyapatite layer or fluorine hydroxyl phosphorus in micro-arc oxidation films layer surface using electrochemical deposition method again Grey rock layers, finally form polylactic acid layers in hydroxyapatite layer or fluorine hydroxyapatite layer surface impregnation;The micro-arc oxidation Differential arc oxidation liquid used is constituted:8~12g/L Na2SiO3, 8~12g/L Na3PO4, 6~10g/L NaOH, 3~7g/L KF, 3~8g/L Na2CO3, 1~5g/L KOH, 50~100mL/L absolute ethyl alcohols, solvent is deionized water, pH value nature;It is described Electrochemical deposition liquid composition is used by hydroxyapatite layer:0.042mol/L Ca(NO3)2、0.5mol/L NaNO3、 0.025mol/L NH4H2PO4, 30-50mL/L absolute ethyl alcohols, 30-50mL/L hydrogen peroxide, 0.004-0.006mol/L alkyl phenols gather Oxygen vinethene OP-21,0.1-0.2mol/L trisodium citrate, solvent is deionized water, is with trometamol and nitre acid for adjusting pH 4.3-4.5;The fluorine hydroxyapatite layer electrochemical deposition liquid is to be added in electrochemical deposition liquid used by hydroxyapatite layer Concentration 0.0008mol/L NaF.
2. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the differential arc oxidation film layer thickness is 20 μ M~30 μm, the hydroxyapatite layer or fluorine hydroxyapatite layer thickness are 4 μm~6 μm.
3. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the differential arc oxidation film layer is by such as lower section It is prepared by method:With described magnesium alloy abutment of implant as anode, stainless steel is negative electrode, is 550 in frequency in differential arc oxidation liquid ~650Hz, the differential of the arc time is 15~30min, and dutycycle is 15~30%, and current density is 20A/cm2, operation temperature is room temperature Under the conditions of carry out differential arc oxidation reaction, reaction takes out magnesium alloy abutment of implant after terminating, and is cleaned by ultrasonic in deionized water, Dried in 20-45 DEG C of baking oven, obtain the magnesium alloy abutment of implant that surface forms differential arc oxidation film layer.
4. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the hydroxyapatite layer or fluorine hydroxyl Apatite layer is prepared as follows:The magnesium alloy abutment of implant of differential arc oxidation film layer is formed as working electrode with surface, platinum Used as to electrode, used as reference electrode, in electrochemical deposition liquid, constant current mode, current density is 4- to saturated calomel electrode to piece 6mA/cm2, after depositing temperature under conditions of 37 DEG C to carry out electrochemical deposition 90-150min, by described magnesium alloy implant Matrix is taken out, and is washed with deionized water only, and room temperature is dried;Immerse again in the NaOH aqueous solution of 1-2mol/L, 2- is soaked at 80 DEG C 4h, is then cleaned repeatedly with deionized water, after room temperature is dried, carries out height in tube furnace under argon gas or vacuum protection atmosphere Temperature annealing, 200 DEG C are warming up to the speed of 10 DEG C/min, are incubated 2h, are obtained surface and are sequentially formed hydroxyl phosphorus from outside to inside Grey rock layers or fluorine hydroxyapatite layer, the magnesium alloy abutment of implant of micro-arc oxidation films Rotating fields.
5. magnesium alloy as claimed in claim 1 implantation composite material, it is characterised in that the thickness of the polylactic acid layers is 5 μm~ 10μm。
6. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the polylactic acid layers are made as follows It is standby:PLA is added in dichloromethane, room temperature uniform stirring 6 hours, obtains the PLA solution of mass concentration 2.5%;Will Surface sequentially forms hydroxyapatite layer or fluorine hydroxyapatite layer, the magnesium alloy implant base of differential arc oxidation film layer from outside to inside In body immersion PLA solution, after soaking at room temperature 20-30s, proposed with the constant speed of 15-25mm/min, in ventilating kitchen interior room Temperature is dried, and then deionized water is cleaned, and room temperature is dried, that is, obtain and sequentially form from outside to inside polylactic acid layers, hydroxyapatite layer Or the magnesium alloy implantation composite material of fluorine hydroxyapatite layer, micro-arc oxidation films Rotating fields.
7. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the magnesium alloy abutment of implant is by such as It is prepared by lower section method:(1) impaired bone structure is carried out into CT scan, obtains the CT scan data of impaired bone structure, and be input to Materialise 3 d modeling softwares, carry out threshold value division, and the noise for importing image is then removed using region growth method, enter The removal of row redundant data, segmentation both injured bones structural region;(2) obtained by Materialise 3 d modeling softwares opening operation The three-dimensional structure data of impaired bone structure, the three-dimensional structure data that then will be obtained is input into UG softwares, obtains digitlization Cranial defect Threedimensional model;(3) according to digitlization Cranial defect threedimensional model, Cranial defect module is designed using CAD software, obtains STL models; (4) by STL mode input 3D printing equipment, then magnesium alloy powder is well mixed in ball mill, mill rotating speed is 250r/min, Ball-milling Time is 30min, and it is protective gas to employ nitrogen as, and obtains the magnesium alloy powder after ball milling;By the magnesium alloy after ball milling Powder adds 3D printing equipment, is molded using laser 3D printing, and the power of laser is 100~200W, sweep speed 20m/min, 1~3ms of pulsewidth, frequency 0.0Hz, 2~3mm of defocusing amount, spot diameter 0.2mm, print under argon gas or vacuum protection atmosphere, single Layer print thickness 0.04mm, the embryo material of acquisition is placed in electrolytic cell of the electrochemical workstation equipped with agitating device, is thrown in electrolytic cell Light liquid is volume ratio 1:9 perchloric acid, the mixed liquor of absolute ethyl alcohol, in 30V constant voltage modes, liquid feeding nitrogen is cooled to -5 DEG C, is stirring Mix and carry out under conditions of 100~200r/min of speed electrochemical polish operation, obtain the embryo material after electrochemical polish, then use successively Absolute alcohol, acetone and deionized water are cleaned by ultrasonic, and dry at room temperature, obtain described magnesium alloy abutment of implant.
8. magnesium alloy as claimed in claim 1 is implanted into composite material, it is characterised in that the magnesium alloy powder is AZ91D magnesium alloys Powder, particle diameter is 120 μm~150 μm.
9. magnesium alloy described in a kind of claim 1 is implanted into the preparation method of composite material, it is characterised in that methods described is: (1) impaired bone structure is carried out into CT scan, obtains the CT scan data of impaired bone structure, and it is three-dimensional to be input to Materialise Modeling software, carries out threshold value division, and the noise for importing image is then removed using region growth method, carries out going for redundant data Except, segmentation both injured bones structural region;(2) the three of impaired bone structure are obtained by Materialise 3 d modeling softwares opening operation Dimension structured data, the three-dimensional structure data that then will be obtained is input into UG softwares, obtains digitlization Cranial defect threedimensional model;(3) root According to digitlization Cranial defect threedimensional model, Cranial defect module is designed using CAD software, obtain STL models;(4) by powder of stainless steel It is well mixed in ball mill, mill rotating speed is 250r/min, and Ball-milling Time is 30min, and it is protective gas to employ nitrogen as, Obtain the magnesium alloy powder after ball milling;By STL mode input 3D printing equipment, the magnesium alloy powder after ball milling is added into 3D printing Equipment, is molded using laser 3D printing, and the power of laser is 100~200W, sweep speed 20m/min, 1~3ms of pulsewidth, frequency 0.0Hz, 2~3mm of defocusing amount, spot diameter 0.2mm, print, individual layer print thickness under argon gas or vacuum protection atmosphere 0.04mm, the embryo material of acquisition is placed in electrolytic cell of the electrochemical workstation equipped with agitating device, and polishing fluid is volume in electrolytic cell Than 1:9 perchloric acid, the mixed liquor of absolute ethyl alcohol, in 30V constant voltage modes, liquid feeding nitrogen is cooled to -5 DEG C, low whipping speed 100~ Electrochemical polish operation is carried out under conditions of 200r/min, the embryo material after electrochemical polish is obtained, then uses absolute alcohol, third successively Ketone and deionized water are cleaned by ultrasonic, and dry at room temperature, obtain described magnesium alloy abutment of implant;(5) with described magnesium alloy Abutment of implant is anode, and stainless steel is negative electrode, in differential arc oxidation liquid, frequency be 550~650Hz, the differential of the arc time be 15~ 30min, dutycycle is 15~30%, and current density is 20A/cm2, operation temperature is that to carry out differential arc oxidation anti-under room temperature condition Should, reaction takes out magnesium alloy abutment of implant after terminating, and is cleaned by ultrasonic in deionized water, is dried in 20-45 DEG C of baking oven, The magnesium alloy abutment of implant that surface forms micro-arc oxidation films Rotating fields is obtained, magnesium alloy abutment of implant/differential arc oxidation is designated as Film layer;(6) with step (5) magnesium alloy abutment of implant/differential arc oxidation film layer as working electrode, platinized platinum is used as to electrode, saturation Used as reference electrode, in electrochemical deposition liquid, constant current mode, current density is 4-6mA/cm to calomel electrode2, depositing temperature is After carrying out electrochemical deposition 90-150min under conditions of 37 DEG C, described magnesium alloy abutment of implant/differential arc oxidation film layer is taken Go out, be washed with deionized water only, room temperature is dried;Immerse again in the NaOH aqueous solution of 1-2mol/L, 2-4h is soaked at 80 DEG C, then Cleaned repeatedly with deionized water, after room temperature is dried, carry out high annealing in tube furnace under argon gas or vacuum protection atmosphere Treatment, 200 DEG C are warming up to the speed of 10 DEG C/min, are incubated 2h, obtain surface sequentially form from outside to inside differential arc oxidation film layer, The magnesium alloy abutment of implant of hydroxyapatite layer or fluorine hydroxyapatite Rotating fields, is designated as magnesium alloy abutment of implant/differential of the arc Oxidation film layer/hydroxyapatite layer or fluorine hydroxyapatite layer;(7) PLA is added in dichloromethane, room temperature is uniformly stirred Mix 6 hours, obtain the PLA solution of mass concentration 2.5%;Magnesium alloy abutment of implant/differential arc oxidation prepared by step (6) In film layer/hydroxyapatite layer or fluorine hydroxyapatite layer immersion PLA solution, after soaking at room temperature 20-30s, with 15-25mm/ The constant speed of min proposes that room temperature is dried in ventilating kitchen, and then deionized water is cleaned, and room temperature is dried, that is, obtain from outside to inside Sequentially form the magnesium alloy implant of polylactic acid layers, hydroxyapatite layer or fluorine hydroxyapatite layer, micro-arc oxidation films Rotating fields Composite.
10. application of the magnesium alloy implantation composite material in bone renovating material is prepared described in a kind of claim 1.
CN201611262987.XA 2016-12-30 2016-12-30 A kind of magnesium alloy is implanted into composite material and its preparation and application Pending CN106902391A (en)

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CN112077308A (en) * 2020-08-27 2020-12-15 西安理工大学 Preparation method of 3D printing porous lattice structure with corrosion resistance and high strength
CN112675362A (en) * 2020-12-24 2021-04-20 上海纳米技术及应用国家工程研究中心有限公司 Preparation method of personalized magnesium alloy bracket for bone repair and product thereof
RU2809685C1 (en) * 2023-05-23 2023-12-14 Федеральное государственное бюджетное учреждение науки Институт химии Дальневосточного отделения Российской академии наук (ИХ ДВО РАН) Method for producing corrosion-resistant hybrid coatings on magnesium and its alloys

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