CN109620475A - One kind being implanted into preparation based on CT data individuation porous titanium alloy shin bone - Google Patents
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/28—Bones
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/28—Bones
- A61F2002/2892—Tibia
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
- A61F2002/30948—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using computerized tomography, i.e. CT scans
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2/3094—Designing or manufacturing processes
- A61F2002/3097—Designing or manufacturing processes using laser
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- Health & Medical Sciences (AREA)
- Orthopedic Medicine & Surgery (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
- Materials For Medical Uses (AREA)
Abstract
One kind being implanted into preparation based on CT data individuation porous titanium alloy shin bone, step: using patient body as original design foundation, medical image tomoscan is carried out to patient's region of interest with CT, data import medical image software, progress Threshold segmentation, region increase, gap is filled up, the flow processing of three-dimensional computations image, obtain required tissue Digitized Structure model；Model is carried out according to medical requirement to simulate the acquisition of deep and morphological parameters, Design of digital software is utilized to carry out the optimization design of implant cast；Laser fast forming preparation.The process design of the invention is scientific and reasonable, the porous titanium alloy implant of preparation is controllable with structure and density, has enough stiffness and strength again, guarantee to deform destruction after it is implanted in vivo, ensure that its elasticity modulus is substantially suitable with the elasticity modulus of skeleton simultaneously, it can preferably be engaged with host bone, stress shielding is prevented, is had wide practical use in medical domain.
Description
Technical field
The invention belongs to Porous Metals Used as Biomaterials preparation technical field, it is related to a kind of porous titanium alloy implant
Preparation method more particularly to a kind of preparation method based on CT data individuation porous titanium alloy shin bone implant.
Background technique
Titanium alloy implant is with its good biocompatibility, and excellent corrosion resistance under physiological environment, synthesis
Mechanics and processing performance, are clinically more and more widely used, be increasingly becoming artificial knee joint, hip joint, shin bone,
The human bodies such as dental implant hard tissue repair and alternative materials.The implant traditional preparation methods are using standardization and module
Change the solid implant of design, manufacturing process uses moldings formed therefrom or numerical control modularized production, does not account for of different patients
Property difference, can directly contribute that individual suitability is poor in use, and the covering of implant and osteotomy surface is not complete in art or mistake
Degree covering, postoperative also to bring activity trajectory and stress abnormal, the risk for increasing implant abrasion, loosening.Meanwhile solid titanium
Alloy implant, rigidity property are far longer than itself bone, can cause " stress shielding " effect, cannot stimulate surrounding well
The growth of bone tissue, cause between implant-host bone without enough, be intermeshed fixation to chronicity, easily cause and loosen,
Cause implant service life to reduce, is always the technical field urgent problem to be solved.
After searching and discovering the prior art, " Ti industry progress " periodical 2 phases of volume 33 in 2016,46-47 pages, open
" powder metallurgy process prepares hollow porous titanium parts " article is delivered, it was recently reported that POROUS TITANIUM generallys use the preparation of powder metallurgy
Method and technique, compacting and subsequent sintering process including titanium valve can be clearly apparent between macrovoid by micro- sem observation
Connected network and titanium particle between small residual porosity, thus there is the part good permeability can be used to manufacture
The medical implant of medicine is carried, but is sintered in the technique sintering process, it is difficult to control the size of setting rate and stomatal limiting value, therefore
It is difficult to prepare the porous structure with uniform pore size and porosity, and is difficult to obtain complex-shaped porous implant
Component；" functional material " periodical 11 phases of volume 40 in 2009, have published " discharge plasma sintering preparation by 1892-1899 pages
Bio-medical porous titanium and its performance study " article, it was recently reported that successfully prepared three-dimensional company using discharge plasma sintering method
Logical POROUS TITANIUM, porosity be 72.5%~83%, compression strength be 10.3~51.8MPa, elasticity modulus be 0.32~
The mechanical property of 1.25GPa and reticular substance bone is close, and has good bioactivity.But preparing porous metal material
During higher cost, and must carry out under vacuum conditions, actual process operation difficulty degree is larger；Patent
CN201510712170.7 " a kind of medical porous tantalum metal material ", discloses using chemical vapor deposition method, by tantalum metal
Compound is reduced to tantalum metal powder, and uniform deposition forms tantalum coating process in porous silica material rack surface, with high porosity >
70%, elasticity modulus < 30Gpa can be used for human body weight bearing bone or non-weight bearing position Permanent implantation material, but this method technological operation
Degree-of-difficulty factor is big, deposition velocity is slow and high production cost, to limit it in the extensive utilization of medical field；Patent
CN201110344241.4 " a kind of preparation method of complicated shape bio-medical porous titanium molybdenum alloy implant ", discloses one kind
Quickly prepare complicated shape bio-medical porous titanium molybdenum alloy implant method, using titanium, molybdenum element powders with it is organic
The mixture of polymeric powder is raw material, passes through three-dimensional modeling, selective laser sintering Quick-forming, thermal debinding and vacuum-sintering
Etc. techniques, prepare bio-medical porous titanium molybdenum alloy implant, do not relate to implant entity part and hollow-out parts set up separately
Meter method, while titanium maxter alloy powder higher cost, and biocompatibility is poor compared with pure titanium metal.
To sum up, the titanium alloy implant of clinical application at present is still using the solid implantation of standardization and modularized design
Body, manufacturing process use moldings formed therefrom or numerical control modularized production, do not account for the personalized difference of different patients, using
Cheng Zhonghui directly contributes that individual suitability is poor, and the covering of implant and osteotomy surface is complete in art or excessive covering, it is postoperative can also band
Carry out activity trajectory and stress is abnormal, the risk for increasing implant abrasion, loosening.Meanwhile solid titanium alloy implant, rigidity
Performance is far longer than itself bone, can cause " stress shielding " effect, cannot stimulate the growth of bone tissue well, cause
Without enough, be intermeshed fixation to chronicity, easily causing and loosening, cause implant using the longevity between implant-host bone
Life is reduced.In addition, titanium alloy implant does not have bioactivity, and the combination of bone is that a kind of machinery is sealed, long-term (or face
When) directly contacted with tissue, cell or blood, the characteristic on surface by implant surrounding tissue function and property generate it is certain
It influences, it would be possible to cause that the reaction such as toxicity, inflammation, thrombus occurs in organism, influence patient body health and lives safety.
Therefore, it is necessary to new titanium alloy implant design method and preparation approach be explored, from medical titanium alloy implantation Antibody Production Techniques
Development from the point of view of, be based on CT data, porous titanium alloy implant Individual design and its rapid prototyping technology, be at present most have it is wide
Prospect and the new way for most having application value.
Summary of the invention
It is scientific and reasonable based on CT data individuation that technical problem to be solved by the invention is to provide a kind of technological designs
Porous titanium alloy shin bone is implanted into preparation, and the implant of preparation has enough stiffness and strength, is unlikely to deform, while bullet
Property modulus is substantially suitable with the elasticity modulus of skeleton, can preferably engage with host bone.
The technical scheme of the invention to solve the technical problem is: a kind of closed based on CT data individuation POROUS TITANIUM
Golden shin bone is implanted into preparation, it is characterised in that the following steps are included:
One, using patient body as original design foundation, medical image tomography is carried out to patient's region of interest with CT and is swept
It retouches, data import medical image software, carry out Threshold segmentation, region increases, gap is filled up, at the process of three-dimensional computations image
Reason, obtains required tissue Digitized Structure model；
Two, tissue Digitized Structure model is carried out according to medical requirement simulating the acquisition of deep and morphological parameters, benefit
The optimization design of implant cast is carried out with Design of digital software；
1) Materialise Mimics Software Create regular octahedron unit is utilized；
2) regular octahedron unit is transformed into internal porous model, and by plane and space array, generates space just
Octahedra porous structure model, i.e. regular octahedron minus cellular construction；
3) shin bone implant physical model (shin bone stem portion) and space regular octahedron porous structure are subjected to boolean and subtract fortune
It calculates, obtains the porous shin bone implant CAD model with shin bone implant surface and regular octahedron porous character；
4) CAD model is converted into STL model with Materialise Mimics software, the pre- place for SLM manufacture
Reason；
Three, prepared by laser fast forming
Using the Ti6Al4V powder of gas atomization preparation as raw material, using laser fusion rapid molding technique, laser fusing is fast
The molding technological parameter of speed are as follows: 140~160W of laser power, 300~500mm/s of scanning speed, sweep span 0.07~
0.09mm forms 0.02~0.04mm of thickness, using orthogonal fault scanning strategy；
Four, differential arc oxidation film layer post-processing is carried out to the prosthesis structure that laser forming obtains, it is porous needed for final acquisition
Titanium alloy muscles and bones implant.
Further, the step 1) tomoscan using 16 row's CT system of Siemens's Sensation type, scanning
The spacing of faultage image is 1mm.
Further, side length a=0.9~1.1mm of the regular octahedron unit of the step 1), strut diameter d=0.30~
0.40mm。
Preferably, the side length a=1mm of the regular octahedron unit, strut diameter d=0.35mm.
It is preferred that the step 3) in Ti6Al4V powder apparent density be 2.5~2.6g/cm3, the partial size model of powder
It is trapped among between 15.34 μm~77.28 μm, average grain diameter is about 27~28 μm, and is in normal distribution trend, and has 70% powder
Partial size is less than 31.32 μm.
It is preferred that the step 3) in laser fast forming preparation process: laser power 150W, scanning speed 400mm/
S, sweep span 0.08mm form thickness 0.03mm.
Further, the step 4) in differential arc oxidation film layer post-processing include differential arc oxidation, alkali heat-treatment, pre-calcification
Processing.
Further, the forward voltage of the differential arc oxidation uses 350V and 1000Hz, and oxidization time is 14~16min.
Further, the alkali heat-treatment is that negatively charged group is introduced pure titanium surface, makes pure titanium surface in negative electricity
Property, by attracting the positive charge Ca in simulated body fluid (SBF)2+、P5+, hydroxyapatite active membrane layer is formed on surface.
Finally, the pre-calcification processing is to put the sample after alkali heat-treatment into 1.0mol/L Na2HP0410h- in solution
For 24 hours, then in saturation Ca (0H)23h-5h is impregnated in solution, hydroxyapatite film layer average thickness reaches 13 μm.
Compared with the prior art, the advantages of the present invention are as follows: it will be using patient body as original design foundation, with CT pairs
Patient's region of interest carry out medical image tomoscan, data import medical image software, carry out Threshold segmentation, region increase,
The flow processing of the images such as gap fills up, three-dimensional computations, obtains required tissue Digitized Structure model, further according to medicine
It is required that carrying out simulating the acquisition of deep and morphological parameters to model, set using the optimization that Design of digital software carries out implant cast
Meter determines model major parameter according to skeletal form parameter acquisition result, carries out feature foundation, curved surface suture, profile optimization, reality
The operation such as body, and then complete the Individual design of porous implant；Meanwhile, it is capable to by adjusting pore size, porosity etc.
Parameter controls the density of implant, and designed porous titanium alloy implant is controllable with structure and density, have again enough
Stiffness and strength, guarantee to deform destruction after it is implanted in vivo, can preferably be engaged with host bone, prevent from answering
Power shielding, has wide practical use in medical domain.
Detailed description of the invention
Fig. 1 is patient's injury two dimension tomograph that CT scan provided by the invention obtains；
Fig. 2 is to carry out CT 3-dimensional reconstruction patient damaged part (shin bone) figure using computer；
.1~3.2 Fig. 3 are respectively the entity shin bone and fills unit trrellis diagram after optimized segmentation；
.1~4.3 Fig. 4 are respectively porous titanium alloy shin bone figure；
Wherein: it is shin bone central porous structure chart that figure, which is 4.1, and Fig. 4 .2 is shin bone shell reinforcing layer figure, and Fig. 4 .3 is optimization
Shin bone figure.
Specific embodiment
The present invention will be described in further detail below with reference to the embodiments of the drawings.
One kind being implanted into preparation, step based on CT data individuation porous titanium alloy shin bone are as follows:
One, using patient body as original design foundation, medical image tomography is carried out to patient's region of interest with CT and is swept
It retouches, as shown in Figure 1, data import medical image software, carries out Threshold segmentation, region increases, gap is filled up, three-dimensional computations image
Flow processing, obtain required tissue Digitized Structure model, such as Fig. 2；
Two, tissue Digitized Structure model is carried out according to medical requirement simulating the acquisition of deep and morphological parameters, benefit
The optimization design of implant cast, such as Fig. 3 are carried out with Design of digital software；
1) Materialise Mimics Software Create regular octahedron unit, unit side length a=1mm, strut diameter d are utilized
=0.35mm；
2) regular octahedron unit is transformed into internal porous model, as shown in figure 4, and by plane and space array,
Generate space regular octahedron porous structure model, i.e. regular octahedron minus cellular construction；
3) shin bone implant physical model (shin bone stem portion) and space regular octahedron porous structure are subjected to boolean and subtract fortune
It calculates, obtains the porous shin bone implant CAD model with shin bone implant surface and regular octahedron porous character；
4) CAD model is converted into STL model with Materialise Mimics software, the pre- place for SLM manufacture
Reason；
Three, prepared by laser fast forming
Using the Ti6Al4V powder of gas atomization preparation as raw material, the apparent density of Ti6Al4V powder is 2.55g/cm3, powder
For the particle size range at end between 15.34 μm~77.28 μm, average grain diameter is about 27.86 μm, and is in normal distribution trend, and have
70% powder diameter is less than 31.32 μm, and used Ti6Al4V powder sphericity is high, and powder diameter is small, good fluidity it is excellent
Point is suitble to selective laser fusing (SLM) molding；
The two most important factors of the scanning speed and sweep span of laser fusion rapid molding form SLM high-densit
The influence of part, laser power 150W, scanning speed 400mm/s, sweep span 0.08mm form thickness 0.03mm, using just
Fault scanning strategy is handed over, part consistency can be made to reach 98.65%, surface roughness reaches 6.27 μm；SLM forms Ti6Al4V
The microhardness of part is HV1 330 or so；After heat treatment, tensile strength 1196.22MPa, yield strength are
1038.92MPa, elongation percentage are promoted to 10.22%, meet standard requirements；The molding Ti6Al4V part average corrosion electric current of SLM
Density is 582.7nA/cm2, after heat treatment it is decreased to 529.8nA/cm2, corrosion resistance be higher than casting standard, meet people
The application of work implant needs；
Four, the prosthesis structure that laser forming obtains is carried out at differential arc oxidation film layer post-processing, including differential arc oxidation, alkali heat
Reason, pre-calcification processing, it is final to obtain required porous titanium alloy muscles and bones implant, such as Fig. 4.
The specific operation process post-processed below to laser fast forming and differential arc oxidation film layer is specifically illustrated:
1) it is handled according to CT scan three-dimensional data, and carries out three-dimensional reconstruction, design the implantation of shin bone porous titanium alloy
Body prosthesis structure melts direct manufacturing technology and process optimization by selective laser, determines optimal processing parameter city sweep span s
When=0.08mm, scanning speed 400mm/s, laser power 150W, powder trend are completely melt, melt road in surface tension and capillary
The effect of pipe power is lower to be tended to be completely combined, and it is 98.65% that consistency, which reaches maximum value, and product surface quality and mechanical property are preferable.
2) differential arc oxidation film layer post-processing is carried out to the prosthesis structure that laser forming obtains, differential arc oxidation forward voltage uses
350V and 1000Hz, oxidization time 15min, oxidation film layer quality is preferable at this time, and film surface micropore is comparatively fine, about 2 μ of aperture
m；After micro-arc oxidation treatment, one layer can be formed in component surface and be conducive to the sticking of osteoblast, the porous knot of differentiation and growth
Structure；The film layer is metal oxide ceramic, and good biocompatibility also has good influence to bone uptake；However, the film layer
Induce the ability of apatite deposition poor, bioactivity is poor, it is difficult to meet clinical requirement, it is therefore necessary at alkali heat
Reason, improves film layer and is optimized.
3) it is in elecrtonegativity that negatively charged group is introduced the pure titanium surface surface Shi Chuntai by alkali heat-treatment, is simulated by attracting
Positive charge Ca in body fluid (SBF)2+、P5+, hydroxyapatite active membrane layer is formed on surface, so that the biology for increasing pure titanium is living
Property.In addition, to the sample of alkali heat-treatment, will also carry out pre-calcification processing to shorten the formation time of film layer induction apatite.
Put the sample after alkali heat-treatment into 1.0mol/L Na2HP0410h-24h in solution, then in saturation Ca (0H)2It is impregnated in solution
3h-5h, hydroxyapatite film layer average thickness reach 13 μm, and surface-active is preferable.
By above-mentioned technique, precision is prepared less than 0.01mm, 70 μm of arc maintenance oxidation film layer thickness, spatial induction hydroxyl phosphorus
Porous, controllable, the active titanium alloy implant of 13 μm of grey rock layers average thickness, in conjunction with Physico-chemical tests as a result, carrying out comprehensive analysis
With evaluation, corresponding technological specification and technical standard are formed, verifies the technology in the feasible of orthopaedics implantation titanium alloy material application
Property, it is the application that porous titanium alloy implant is implanted into field in orthopaedics, material foundation and technical support is provided.
Claims (10)
1. one kind is implanted into preparation based on CT data individuation porous titanium alloy shin bone, it is characterised in that including following step
It is rapid:
One, using patient body as original design foundation, medical image tomoscan, number are carried out to patient's region of interest with CT
According to medical image software is imported, progress Threshold segmentation, region increase, gap is filled up, the flow processing of three-dimensional computations image, obtain
Required tissue Digitized Structure model；
Two, tissue Digitized Structure model is carried out according to medical requirement simulating the acquisition of deep and morphological parameters, utilizes number
The optimization design of word design software progress implant cast；
1) Materialise Mimics Software Create regular octahedron unit is utilized；
2) regular octahedron unit is transformed into internal porous model, and by plane and space array, generates the positive octahedral in space
Body porous structure model, i.e. regular octahedron minus cellular construction；
3) shin bone implant physical model (shin bone stem portion) and space regular octahedron porous structure are subjected to Boolean subtraction calculation, obtained
To the porous shin bone implant CAD model with shin bone implant surface and regular octahedron porous character；
4) CAD model is converted into STL model with Materialise Mimics software, the pretreatment for SLM manufacture；
Three, prepared by laser fast forming
Using the Ti6Al4V powder of gas atomization preparation as raw material, using laser fusion rapid molding technique, laser fusing is fast rapid-result
The technological parameter of type are as follows: 140~160W of laser power, 300~500mm/s of scanning speed, 0.07~0.09mm of sweep span, at
Type 0.02~0.04mm of thickness, using orthogonal fault scanning strategy；
Four, differential arc oxidation film layer post-processing is carried out to the prosthesis structure that laser forming obtains, POROUS TITANIUM needed for final acquisition is closed
Golden muscles and bones implant.
2. preparation method according to claim 1, it is characterised in that: the step 1) tomoscan using west
The sub- 16 row's CT system of Sensation type of door, the spacing for scanning faultage image is 1mm.
3. preparation method according to claim 1, it is characterised in that: the side length a of the regular octahedron unit of the step 1)
=0.9~1.1mm, strut diameter d=0.30~0.40mm.
4. preparation method according to claim 3, it is characterised in that: the side length a=1mm of the regular octahedron unit, branch
Column diameter d=0.35mm.
5. preparation method according to claim 1, it is characterised in that: the step 3) in Ti6Al4V powder pine dress
Density is 2.5~2.6g/cm3, for the particle size range of powder between 15.34 μm~77.28 μm, average grain diameter is about 27~28 μ
M, and be in normal distribution trend, and have 70% powder diameter less than 31.32 μm.
6. preparation method according to claim 1, it is characterised in that: the step 3) in laser fast forming preparation
Technique: laser power 150W, scanning speed 400mm/s, sweep span 0.08mm form thickness 0.03mm.
7. preparation method according to claim 1, it is characterised in that: the step 4) in differential arc oxidation film layer after
Reason includes differential arc oxidation, alkali heat-treatment, pre-calcification processing.
8. preparation method according to claim 7, it is characterised in that: the forward voltage of the differential arc oxidation using 350V and
1000Hz, oxidization time are 14~16min.
9. preparation method according to claim 7, it is characterised in that: the alkali heat-treatment is to draw negatively charged group
Enter pure titanium surface, makes pure titanium surface in elecrtonegativity, by attracting the positive charge Ca in simulated body fluid (SBF)2+、P5+, in surface shape
At hydroxyapatite active membrane layer.
10. preparation method according to claim 7, it is characterised in that: the pre-calcification processing is will be after alkali heat-treatment
Sample puts 1.0mol/L Na into2HPO410h-24h in solution, then in saturation Ca (OH)23h-5h, hydroxy-apatite are impregnated in solution
Stone film layer average thickness reaches 13 μm.
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
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| CN110528048A (en) * | 2019-08-30 | 2019-12-03 | 广东省新材料研究所 | A kind of titanium alloy implant Bio-surface active coating and preparation method thereof |
| CN110680567A (en) * | 2019-11-07 | 2020-01-14 | 江苏科技大学 | Method and system for manufacturing porous tibial implant |
| CN111728742A (en) * | 2020-06-30 | 2020-10-02 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN113634765A (en) * | 2021-08-06 | 2021-11-12 | 北京航空航天大学 | Medical titanium alloy implant manufactured by additive manufacturing and surface impact strengthening method |
| CN114886617A (en) * | 2022-04-11 | 2022-08-12 | 汕头大学 | Preparation method of space filling curve type porous implant and implant |
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2018
- 2018-11-13 CN CN201811342651.3A patent/CN109620475A/en active Pending
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN110528048A (en) * | 2019-08-30 | 2019-12-03 | 广东省新材料研究所 | A kind of titanium alloy implant Bio-surface active coating and preparation method thereof |
| CN110680567A (en) * | 2019-11-07 | 2020-01-14 | 江苏科技大学 | Method and system for manufacturing porous tibial implant |
| CN111728742A (en) * | 2020-06-30 | 2020-10-02 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN111728742B (en) * | 2020-06-30 | 2023-03-10 | 蒋青 | Porous meniscus substitute modeling and preparation method thereof |
| CN113634765A (en) * | 2021-08-06 | 2021-11-12 | 北京航空航天大学 | Medical titanium alloy implant manufactured by additive manufacturing and surface impact strengthening method |
| CN114886617A (en) * | 2022-04-11 | 2022-08-12 | 汕头大学 | Preparation method of space filling curve type porous implant and implant |
| CN114886617B (en) * | 2022-04-11 | 2023-08-18 | 汕头大学 | Preparation method of space filling curve type porous implant and implant |
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