CN102090982A - Artificial tooth root or joint material and microarc oxidation preparation method thereof - Google Patents
Artificial tooth root or joint material and microarc oxidation preparation method thereof Download PDFInfo
- Publication number
- CN102090982A CN102090982A CN 201110023969 CN201110023969A CN102090982A CN 102090982 A CN102090982 A CN 102090982A CN 201110023969 CN201110023969 CN 201110023969 CN 201110023969 A CN201110023969 A CN 201110023969A CN 102090982 A CN102090982 A CN 102090982A
- Authority
- CN
- China
- Prior art keywords
- tooth root
- artificial tooth
- joint
- artificial
- differential arc
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Images
Abstract
The invention discloses an artificial tooth root or joint material capable of releasing zinc and cerium trace elements and having a nano/micron porous surface structure and a microarc oxidation preparation method thereof. The artificial tooth root or joint is prepared from a pure titanium or titanium alloy matrix and a porous titanium dioxide bioactive surface layer, wherein the porous titanium dioxide bioactive surface layer is obtained on the surface of the pure titanium or titanium alloy matrix by using a microarc oxidization technology and doped with the trace zinc and cerium elements, the pore diameter of the porous titanium dioxide bioactive surface layer is changed between 50nm and 500nm, thus the surface bacteriostatic capacity, the bioactivity and the cell regulation and control capacity of the initial implanted surface can be improved remarkably, and multiple beneficial functions are obtained. The preparation method comprises the steps of: firstly processing the artificial tooth root (joint) by selecting pure titanium or titanium alloy; then obtaining the titanium dioxide bioactive surface layer with the nano-micro porous structure on the surface of the artificial tooth root (joint) by adopting a microarc oxidization technology; meanwhile adding zinc and cerium soluble salts to electrolyte and carrying out synchronous doping by utilizing a microarc oxidization process.
Description
Technical field
The present invention relates to the energy release of trace elements and have nanometer or artificial tooth root or the artificial joint and the differential arc oxidation preparation method thereof of micron porous surface structure, particularly relate to by pure titanium or titanium alloy substrate and adopt that differential arc oxidization technique obtains on its surface be doped with trace zinc and Ce elements, aperture to changing artificial tooth root or artificial joint and the differential arc oxidation preparation method thereof that regulatable poriferous titanium dioxide bioactivity surface layer is formed the 500mm, belong to the substitute material for human hard tissues field at 50nm.
Background technology
Substitute material for human hard tissues such as canine implant or artificial joint can recover to lack the function of natural sclerous tissues, and this just makes the damage patient of sclerous tissues that can't repair with traditional method can obtain basic treatment, improves the quality of living.Normally used artificial hard tissue substituting material is a metal material, because of it is a bio-inert material, combines with not forming firm physiology between the body bone tissue, after implantation, usually can become flexible, and causes the displacement failure.In addition, the inefficacy of implanting sclerous tissues can cause complication such as bone resorption, has a strong impact on the late result of artificial substituting tissue.Adopt process for modifying surface to prepare functional living being coating (film), can reduce the stripping of harmful metal ion under the human body environment, improve its biocompatibility and biological activity, and strengthen the implant function at artificial hard tissue substituting metal base surface.
The titanium dioxide ceramic coating has advantages such as low intrinsic bio-toxicity, corrosion-proof wear are functional, chemical inertness, is the excellent protection layer material.Titanium dioxide has excellent biological compatibility and biological in addition, can promote the formation of deposits apatite layer of phosphorus calcium phase material, and cell growth has facilitation.
Loose structure with different apertures affects the performance and the function of coating, makes it become the important place [Surface and Coatings Technology. 2009,204:1126-1131] of drug release, osseous tissue growth, cell adhesion propagation.By to adjustment and control of pore diameter, can change biomedical performance of material surface and function, thereby adapt to different human body environment and satisfy the correlation function demand.
Zinc element is various enzymes and proteic important component part, has the function of biological function actuator.Zinc element is being brought into play important effect aspect the metabolism of bone in addition, the experiment in vitro result shows that zinc can improve the synthetic of DNA in the osteoblast, bone formation and mineralising are had facilitation, and it heavily is absorbed with inhibitory action [The Journal of Nutritional Biochemistry. doi:10.1016/j.jnutbio.2010.01.003] to bone simultaneously.
Trace element cerium and health have substantial connection, are the indispensable trace element of a kind of human body, have important physical function and pharmacological action widely.Cerium has certain inhibition to people's hepatocarcinoma, laryngeal carcinoma, leukemia etc., cerium can separate it by softening cell wall, and protoplasm is overflowed, and then reach the purpose of bacteria growing inhibiting, simultaneously the activity that Ce elements can superoxide dismutase enhancement SOD lures that the active oxygen of peroxide reactions becomes ground state oxygen and hydrogen peroxide into, thereby delays the aging of cell.In addition, cerium also has effects such as mutation, conjugated protein, immunomodulating, can the different biological effects of performance under variable concentrations, and some germ killing drugs that contain cerium have at present entered clinical trial.
Demonstrate huge biomedical applications potentiality by differential arc oxidization technique in the porous ceramics coating of titanium alloy substrate surface preparation biologically active.Yet, so far do not see by can discharge simultaneously zinc and cerium trace element and surface have the aperture at 50nm to changing the artificial tooth root that regulatable poriferous titanium dioxide bioactivity surface layer forms or the report of artificial joint and differential arc oxidation preparation method thereof the 500mm, and studies show that the surface pore structure from nanometer to the micron different scale has tremendous influence to the bio-medical performance that sclerous tissues replaces biomaterial.Titanium dioxide itself does not have functions such as sterilization, cell adjusting, is subjected to very big restriction in actual applications.Surface energy release of trace elements and the artificial tooth root (joint) with nano/micron porous surface structure can effectively remedy above-mentioned disappearance.Given this, draw the present invention.
Summary of the invention
Technical problem:The objective of the invention is at the above-mentioned deficiency of artificial hard tissue substituting material-artificial tooth root (joint), proposing a kind of while can discharge zinc and cerium trace element and surface and have the aperture regulatable poriferous titanium dioxide bioactivity surface layer forms to changing between the 500mm at 50nm, can significantly improve implantation initial stage surface bioactive, cell regulate and control ability and have artificial tooth root or the artificial joint and the differential arc oxidation preparation method thereof of multiple beneficial function.
Technical scheme:The artificial tooth root (joint) of can release of trace elements and having a nano/micron porous surface structure the titanium matrix surface have that one deck adopts that differential arc oxidization technique makes up have the aperture at 50nm to changing regulatable poriferous titanium dioxide bioactivity surface layer between the 500mm, this surface layer mixes micro-functional elements zinc and cerium synchronously at the differential arc oxidation building process.Owing in the differential arc oxidation process, when generating oxide layer, puncture high-temperature ceramicsization then, make the titanium dioxide bioactive ceramic coating and the metallic matrix bond strength height of tool nano/micron pore structure; And TiO 2 porous structure has good biological activity and can promote the deposition growing of apatite layer, and the loose structure in different apertures also is the useful place of cell proliferation growth simultaneously; Can improve after zinc element mixes the matrix surface peripheral cell metabolic function, promote the growth of osteocyte and bone resorption had inhibitory action, simultaneously, after mixing, Ce elements can improve the matrix surface antibacterial ability, two kinds of cooperative effects biology that trace-element slow-release produced can usefully mutually be replenished, suppress antibacterial the inflammation that surrounding tissue is produced of initial stage behind artificial tooth root (joint) implant into body, and promote the adhesion, propagation, growth, growth etc. of osteocyte and osseous tissue for a long time.
The present invention is realized by the following technical programs:
This material can release of trace elements and is had nanometer or the porous surface structure of micron, described artificial tooth root or artificial joint by pure titanium or titanium alloy substrate and adopt that the differential arc oxidation processing mode obtains on its surface be doped with trace zinc and Ce elements, aperture are formed to changing regulatable poriferous titanium dioxide bioactivity surface layer the 500mm at 50nm.
The differential arc oxidation preparation method of artificial tooth root of the present invention or joint material is carried out as follows:
1) at first select for use pure titanium or titanium alloy to process the model of artificial tooth root or artificial joint;
2) configuration packet contains the carbonate system special electrolytic solutions of zinc ion and cerium ion;
3) the model surface sanding and polishing of artificial tooth root or artificial joint, model with artificial tooth root or artificial joint in above-mentioned carbonate system special electrolytic solutions is an anode, rustless steel is a negative electrode, adopting the microarc oxidation equipment provided model to artificial tooth root or artificial joint of bipolar pulse to carry out differential arc oxidation handles, make up poriferous titanium dioxide bioactivity surface layer in the titanio surface, change the differential arc oxidation processing parameter and carry out the trace element doping simultaneously with the adjustment aperture size;
4) with the model of above-mentioned taking-up artificial tooth root or artificial joint with ethanol drip washing after, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can release of trace elements and have nanometer or the artificial tooth root or the artificial joint of the porous surface structure of micron.
The carbonate system special electrolytic solutions of being addressed that includes zinc ion and cerium ion includes the Na of 2 ~ 50g/L
2CO
3, 0.5 ~ 5g/L the soluble zinc salt, the solubility cerium salt of 0.1 ~ 10mmol/L of KOH, 0.1 ~ 10mmol/L.
The differential arc oxidation processing mode running voltage range of accommodation of being addressed: forward voltage 200 ~ 1000V, negative voltage 0 ~ 300V, pulse frequency range of accommodation: direct impulse 50Hz ~ 3000Hz, negative-going pulse frequency 1Hz ~ 3000Hz, dutycycle: forward 4% ~ 80%, negative sense 0% ~ 50%, the differential arc oxidation response time is 0.5 ~ 120min.
Beneficial effect:
(1) artificial root of the tooth of the present invention or artificial joint can discharge zinc and cerium trace element simultaneously, zinc element can improve the metabolic function of artificial tooth root (joint) peripheral cell, promote the growth of osteocyte and bone resorption is had inhibitory action, simultaneously, Ce elements can improve artificial tooth root (joint) antibacterial surface ability, two kinds of cooperative effects biology that trace-element slow-release produced can usefully mutually be replenished, suppress antibacterial the inflammation that surrounding tissue is produced of initial stage behind artificial tooth root (joint) implant into body, and promote the adhesion of osteocyte and osseous tissue for a long time, propagation, growth, grow etc.This artificial tooth root (joint) has that good biological activity, cell are regulated, beneficial effect and induced osteogenesis effect such as antibacterial, can form firm physiology with osseous tissue safely and combine.
(2) artificial root of the tooth of the present invention or artificial joint surface titanium dioxide bioactive ceramic coating and metallic matrix bond strength height, and have the aperture at 50nm to changing regulatable ideal nano/micron pore structure between the 500mm: the coating densification that contacts with the metal surface, wear and corrosion behavior excellence, be excellent protection layer structure, and can promote the deposition growing of apatite layer; The nano/micron pore structure helps the load of zinc and cerium trace element, increase contact area with surrounding bone tissue and cell, be again the desirable place of cell adhesion, propagation and growth simultaneously, can change the aperture according to the different demands of implantation environment changes between the 500mm at 50nm, its surperficial zinc element and Ce elements carry out slow release behind the implant into body, have not only had beneficial effect but also scalable implant peripheral cell functions such as antibacterial strong bone.
Description of drawings
Fig. 1 is the phase composition XRD figure spectrum of the multiporous biological active surface layer of the artificial root of the tooth of the present invention, obviously, the multiporous biological active surface layer of the artificial root of the tooth of the present invention is mainly by the titanium dioxide phase composition of titanium dioxide and anatase structured (A) of rutile structure (R).
Fig. 2 obviously, is doped with zinc and two kinds of trace element of cerium simultaneously for the surface chemistry composition energy spectrogram of the artificial root of the tooth of the present invention in the multiporous biological active titanic dioxide surface layer of the artificial root of the tooth of the present invention.
The instantiation mode
Embodiment 1
(1) at first select for use medical pure Ti to process artificial tooth root;
(2) artificial tooth root pretreatment: with artificial tooth root use abrasive paper for metallograph that label is followed successively by 600#, 800#, 1000# by coarse sand to fine sand sanding and polishing step by step, use acetone, 70% ethanol, distilled water ultrasonic cleaning then, dried for standby.
(3) interpolation of the configuration of electrolyte and zinc, Ce elements: adopt the sodium carbonate liquor system, it is the sodium carbonate liquor of 20g/L and the potassium hydroxide solution of 1g/L that configuration 10L contains concentration; Add the zinc chloride of 0.1 ~ 0.5mmol/L and the cerium chloride of 0.1 ~ 0.5mmol/L then, 40 degrees centigrade of constant temperature stirring and dissolving, stand-by;
(4) differential arc oxidation of artificial tooth root and aperture control: artificial tooth root is placed the microarc oxidation equipment provided electrolysis bath of bipolar pulse and adds the electrolyte that configures, with the artificial tooth root is anode, the stainless steel electrolytic groove is a negative electrode, regulates technological parameter artificial tooth root is carried out differential arc oxidation.Technological parameter is: constant voltage mode, running voltage range of accommodation forward voltage 300 ~ 600V, negative voltage 0V, pulse frequency range of accommodation direct impulse 100 ~ 600Hz, dutycycle forward 12%, negative sense 0%, response time 10 ~ 15min.
(5) with after the drip washing of above-mentioned taking-up artificial tooth root usefulness ethanol, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can discharge zinc and cerium trace element and have the artificial tooth root of nano/micron porous surface structure, and its surface layer phase composition is shown in Fig. 1 XRD figure spectrum, its surface chemistry composition can spectrogram as shown in Figure 2.
Embodiment 2
(1) at first select for use the Ti6Al4V alloy to process artificial joint;
(2) artificial joint pretreatment: with artificial joint use abrasive paper for metallograph that label is followed successively by 600#, 800#, 1000# by coarse sand to fine sand sanding and polishing step by step, use acetone, 70% ethanol, distilled water ultrasonic cleaning then, dried for standby.
(3) interpolation of the configuration of electrolyte and zinc, Ce elements: adopt the sodium carbonate liquor system, it is the sodium carbonate liquor of 20g/L and the potassium hydroxide solution of 1g/L that configuration 10L contains concentration; Add the zinc chloride of 0.1 ~ 0.5mmol/L and the cerium chloride of 0.1 ~ 0.5mmol/L then, 40 degrees centigrade of constant temperature stirring and dissolving, stand-by;
(4) differential arc oxidation of artificial joint and aperture control: artificial joint is placed the microarc oxidation equipment provided electrolysis bath of bipolar pulse and adds the electrolyte that configures, with the artificial joint is anode, the stainless steel electrolytic groove is a negative electrode, regulates technological parameter artificial joint is carried out differential arc oxidation.Technological parameter is: constant voltage mode, running voltage range of accommodation forward voltage 300V, negative voltage 0V, pulse frequency range of accommodation direct impulse 400Hz, dutycycle forward 12%, negative sense 0%, response time 3min.
(5) with above-mentioned taking-up artificial joint with ethanol drip washing after, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can discharge zinc and cerium trace element and have the artificial joint of nano/micron porous surface structure.
Embodiment 3
(1) at first select for use medical pure Ti to process artificial tooth root;
(2) artificial tooth root pretreatment: with artificial tooth root use abrasive paper for metallograph that label is followed successively by 600#, 800#, 1000# by coarse sand to fine sand sanding and polishing step by step, use acetone, 70% ethanol, distilled water ultrasonic cleaning then, dried for standby.
(3) interpolation of the configuration of electrolyte and zinc, Ce elements: adopt the sodium carbonate liquor system, it is the sodium carbonate liquor of 20g/L and the potassium hydroxide solution of 1g/L that configuration 10L contains concentration; Add the zinc chloride of 0.1 ~ 0.5mmol/L and the cerium chloride of 0.1 ~ 0.5mmol/L then, 40 degrees centigrade of constant temperature stirring and dissolving, stand-by;
(4) differential arc oxidation of artificial tooth root: artificial tooth root is placed the microarc oxidation equipment provided electrolysis bath of bipolar pulse and adds the electrolyte that configures, with the artificial tooth root is anode, the stainless steel electrolytic groove is a negative electrode, regulates technological parameter artificial tooth root is carried out differential arc oxidation.Technological parameter is: constant voltage mode, running voltage range of accommodation forward voltage 300V, negative voltage 0V, pulse frequency range of accommodation direct impulse 2000Hz, dutycycle forward 26%, negative sense 0%, response time 3min.
(5) with above-mentioned taking-up artificial tooth root with ethanol drip washing after, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can discharge zinc and cerium trace element and have the artificial tooth root of nano/micron porous surface structure.
Embodiment 4
(1) at first select for use the Ti6Al4V alloy to process artificial joint;
(2) artificial joint pretreatment: with artificial joint use abrasive paper for metallograph that label is followed successively by 600#, 800#, 1000# by coarse sand to fine sand sanding and polishing step by step, use acetone, 70% ethanol, distilled water ultrasonic cleaning then, dried for standby.
(3) interpolation of the configuration of electrolyte and zinc, Ce elements: adopt the sodium carbonate liquor system, it is the sodium carbonate liquor of 20g/L and the potassium hydroxide solution of 1g/L that configuration 10L contains concentration; Add the zinc chloride of 0.1 ~ 0.5mmol/L and the cerium chloride of 0.1 ~ 0.5mmol/L then, 40 degrees centigrade of constant temperature stirring and dissolving, stand-by;
(4) differential arc oxidation of artificial joint: artificial joint is placed the microarc oxidation equipment provided electrolysis bath of bipolar pulse and adds the electrolyte that configures, with the artificial joint is anode, the stainless steel electrolytic groove is a negative electrode, regulates technological parameter artificial joint is carried out differential arc oxidation.Technological parameter is: constant voltage mode, running voltage range of accommodation forward voltage 400V, negative voltage 0V, pulse frequency range of accommodation direct impulse 100Hz, dutycycle forward 12%, negative sense 0%, response time 5min.
(5) with above-mentioned taking-up artificial joint with ethanol drip washing after, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can discharge zinc and cerium trace element and have the artificial joint of nano/micron porous surface structure.
Obviously, the above embodiment of the present invention only is in order to clearly demonstrate example of the present invention, and is not to be qualification to embodiments of the present invention.For those of ordinary skill in the field; also can make other changes in different forms on the basis of the above description; here need not also can't give all embodiments exhaustive, and these belong to conspicuous variation or the change that spirit of the present invention amplified out and still are in protection scope of the present invention.
Claims (4)
1. artificial tooth root or joint material, it is characterized in that, this material can release of trace elements and is had nanometer or the porous surface structure of micron, described artificial tooth root or artificial joint by pure titanium or titanium alloy substrate and adopt that the differential arc oxidation processing mode obtains on its surface be doped with trace zinc and Ce elements, aperture are formed to changing regulatable poriferous titanium dioxide bioactivity surface layer the 500mm at 50nm.
2. the differential arc oxidation preparation method of artificial tooth root as claimed in claim 1 or joint material is characterized in that artificial tooth root of being addressed or joint preparation method are carried out as follows:
1) at first select for use pure titanium or titanium alloy to process the model of artificial tooth root or artificial joint;
2) configuration packet contains the carbonate system special electrolytic solutions of zinc ion and cerium ion;
3) the model surface sanding and polishing of artificial tooth root or artificial joint, model with artificial tooth root or artificial joint in above-mentioned carbonate system special electrolytic solutions is an anode, rustless steel is a negative electrode, adopting the microarc oxidation equipment provided model to artificial tooth root or artificial joint of bipolar pulse to carry out differential arc oxidation handles, make up poriferous titanium dioxide bioactivity surface layer in the titanio surface, change the differential arc oxidation processing parameter and carry out the trace element doping simultaneously with the adjustment aperture size;
4) with the model of above-mentioned taking-up artificial tooth root or artificial joint with ethanol drip washing after, vacuum drying, the sterilization aseptic preservation in back, standby, get final product to such an extent that the present invention can release of trace elements and have nanometer or the artificial tooth root or the artificial joint of the porous surface structure of micron.
3. the differential arc oxidation preparation method of artificial tooth root according to claim 2 or joint material is characterized in that the carbonate system special electrolytic solutions that includes zinc ion and cerium ion addressed, includes the Na of 2 ~ 50g/L
2CO
3, 0.5 ~ 5g/L the soluble zinc salt, the solubility cerium salt of 0.1 ~ 10mmol/L of KOH, 0.1 ~ 10mmol/L.
4. the differential arc oxidation preparation method of artificial tooth root according to claim 2 or joint material, it is characterized in that the differential arc oxidation processing mode running voltage range of accommodation addressed: forward voltage 200 ~ 1000V, negative voltage 0 ~ 300V, pulse frequency range of accommodation: direct impulse 50Hz ~ 3000Hz, negative-going pulse frequency 1Hz ~ 3000Hz, dutycycle: forward 4% ~ 80%, negative sense 0% ~ 50%, the differential arc oxidation response time is 0.5 ~ 120min.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201110023969A CN102090982B (en) | 2011-01-21 | 2011-01-21 | Artificial tooth root or joint material and microarc oxidation preparation method thereof |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201110023969A CN102090982B (en) | 2011-01-21 | 2011-01-21 | Artificial tooth root or joint material and microarc oxidation preparation method thereof |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN102090982A true CN102090982A (en) | 2011-06-15 |
| CN102090982B CN102090982B (en) | 2012-09-19 |
Family
ID=44124362
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201110023969A Expired - Fee Related CN102090982B (en) | 2011-01-21 | 2011-01-21 | Artificial tooth root or joint material and microarc oxidation preparation method thereof |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN102090982B (en) |
Cited By (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102605411A (en) * | 2012-03-31 | 2012-07-25 | 大连理工大学 | Preparation process of pleated hole-slot shaped titanium dioxide thin film with super wetting ability |
| CN102732882A (en) * | 2012-07-13 | 2012-10-17 | 东南大学 | Artificial joint with micro-nano graded topological surface structure and preparation method of artificial joint |
| CN102747404A (en) * | 2012-07-13 | 2012-10-24 | 东南大学 | Composite film with photocatalytic function and preparation method thereof |
| CN102743789A (en) * | 2012-07-13 | 2012-10-24 | 东南大学 | Artificial tooth root with micro-nano hierarchical topologic surface structure and preparation method of artificial tooth root |
| CN102908661A (en) * | 2012-10-31 | 2013-02-06 | 武汉科技大学 | Medical titanium with a trace element slow-release function or titanium alloy implant material as well as preparation method and application of same |
| CN105458257A (en) * | 2015-12-08 | 2016-04-06 | 南通金源智能技术有限公司 | 3D printing titanium-based composite false tooth |
| CN105965154A (en) * | 2016-06-27 | 2016-09-28 | 梁春永 | Biomedical titanium surface modifying method |
| CN107723778A (en) * | 2017-09-06 | 2018-02-23 | 太原理工大学 | A kind of method for preparing Ni Ti O richness Ni nano-pores in NiTi alloy surfaces |
| CN109432514A (en) * | 2018-12-12 | 2019-03-08 | 西南大学 | Have degradable magnesium alloy bone nail and preparation method that squamous imitates bone nano-structured coating |
| CN110241453A (en) * | 2019-04-25 | 2019-09-17 | 西南大学 | A kind of release fluoride and the degradable kirsite bone nail of cerium and preparation method thereof |
| CN110965108A (en) * | 2019-12-27 | 2020-04-07 | 沈兰兰 | Zn-TiO2Method for producing a coating |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101732762A (en) * | 2010-01-01 | 2010-06-16 | 东南大学 | Bioactive artificial joint capable of slowly releasing trace element selenium |
| CN101745146A (en) * | 2009-12-31 | 2010-06-23 | 东南大学 | Functional artificial joint on surface of cerium-loaded nanotube array and preparation method thereof |
| CN101744666A (en) * | 2010-01-01 | 2010-06-23 | 东南大学 | Artificial tooth root with slow release function of trace element of selenium and preparation method thereof |
-
2011
- 2011-01-21 CN CN201110023969A patent/CN102090982B/en not_active Expired - Fee Related
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101745146A (en) * | 2009-12-31 | 2010-06-23 | 东南大学 | Functional artificial joint on surface of cerium-loaded nanotube array and preparation method thereof |
| CN101732762A (en) * | 2010-01-01 | 2010-06-16 | 东南大学 | Bioactive artificial joint capable of slowly releasing trace element selenium |
| CN101744666A (en) * | 2010-01-01 | 2010-06-23 | 东南大学 | Artificial tooth root with slow release function of trace element of selenium and preparation method thereof |
Cited By (18)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102605411B (en) * | 2012-03-31 | 2014-08-13 | 大连理工大学 | Preparation process of pleated hole-slot shaped titanium dioxide thin film with super wetting ability |
| CN102605411A (en) * | 2012-03-31 | 2012-07-25 | 大连理工大学 | Preparation process of pleated hole-slot shaped titanium dioxide thin film with super wetting ability |
| CN102732882A (en) * | 2012-07-13 | 2012-10-17 | 东南大学 | Artificial joint with micro-nano graded topological surface structure and preparation method of artificial joint |
| CN102747404A (en) * | 2012-07-13 | 2012-10-24 | 东南大学 | Composite film with photocatalytic function and preparation method thereof |
| CN102743789A (en) * | 2012-07-13 | 2012-10-24 | 东南大学 | Artificial tooth root with micro-nano hierarchical topologic surface structure and preparation method of artificial tooth root |
| CN102743789B (en) * | 2012-07-13 | 2014-09-10 | 东南大学 | Artificial tooth root with micro-nano hierarchical topologic surface structure and preparation method of artificial tooth root |
| CN102747404B (en) * | 2012-07-13 | 2014-08-13 | 东南大学 | Composite film with photocatalytic function and preparation method thereof |
| CN102732882B (en) * | 2012-07-13 | 2014-08-13 | 东南大学 | Artificial joint with micro-nano graded topological surface structure and preparation method of artificial joint |
| CN102908661A (en) * | 2012-10-31 | 2013-02-06 | 武汉科技大学 | Medical titanium with a trace element slow-release function or titanium alloy implant material as well as preparation method and application of same |
| CN102908661B (en) * | 2012-10-31 | 2014-06-25 | 武汉科技大学 | Medical titanium with a trace element slow-release function or titanium alloy implant material as well as preparation method and application of same |
| CN105458257A (en) * | 2015-12-08 | 2016-04-06 | 南通金源智能技术有限公司 | 3D printing titanium-based composite false tooth |
| CN105965154A (en) * | 2016-06-27 | 2016-09-28 | 梁春永 | Biomedical titanium surface modifying method |
| CN105965154B (en) * | 2016-06-27 | 2018-06-26 | 梁春永 | A kind of biomedical titanium surface modifying method |
| CN107723778A (en) * | 2017-09-06 | 2018-02-23 | 太原理工大学 | A kind of method for preparing Ni Ti O richness Ni nano-pores in NiTi alloy surfaces |
| CN107723778B (en) * | 2017-09-06 | 2020-01-07 | 太原理工大学 | Method for preparing Ni-Ti-O Ni-rich nano-pores on surface of NiTi alloy |
| CN109432514A (en) * | 2018-12-12 | 2019-03-08 | 西南大学 | Have degradable magnesium alloy bone nail and preparation method that squamous imitates bone nano-structured coating |
| CN110241453A (en) * | 2019-04-25 | 2019-09-17 | 西南大学 | A kind of release fluoride and the degradable kirsite bone nail of cerium and preparation method thereof |
| CN110965108A (en) * | 2019-12-27 | 2020-04-07 | 沈兰兰 | Zn-TiO2Method for producing a coating |
Also Published As
| Publication number | Publication date |
|---|---|
| CN102090982B (en) | 2012-09-19 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN102090982B (en) | Artificial tooth root or joint material and microarc oxidation preparation method thereof | |
| Kung et al. | Bioactivity and corrosion properties of novel coatings containing strontium by micro-arc oxidation | |
| CN102743789B (en) | Artificial tooth root with micro-nano hierarchical topologic surface structure and preparation method of artificial tooth root | |
| CN102146577B (en) | Pure-titanium metal surface micro-arc oxidation treatment electrolyte and antimicrobial bioactive coating preparation method thereof | |
| CN104726921B (en) | Titanium dioxide/hydroxyapatite bioactive nano-composite coating of fluorine containing strontium and its preparation method and application | |
| CN102732882B (en) | Artificial joint with micro-nano graded topological surface structure and preparation method of artificial joint | |
| CN102371005B (en) | Zinc-doped porous nano-titanium oxide coating and its preparation method | |
| CN101054708A (en) | Method of preparing hydroxyl apatite bioceramic film by plasma micro-arc oxidization method | |
| CN108434517A (en) | Antibacterial dental implant and preparation method thereof | |
| CN102049064B (en) | A kind of silicon doping porous nanometer titanium oxide and preparation method thereof | |
| CN101560685B (en) | Method for preparing bioactive coating on titanium alloy surface | |
| CN102747403A (en) | Method of preparing magnesium-doped hydroxyapatite/titania active film on surface of medical titanium alloy | |
| Qiao et al. | Composite coatings of lanthanum-doped fluor-hydroxyapatite and a layer of strontium titanate nanotubes: fabrication, bio-corrosion resistance, cytocompatibility and osteogenic differentiation | |
| Weng et al. | Osteogenic activity, antibacterial ability, and Ni release of Mg-incorporated Ni-Ti-O nanopore coatings on NiTi alloy | |
| CN107761148B (en) | A method of fibroin albumen hydroxyapatite coating layer is prepared in metal surface | |
| CN102921042A (en) | Hard tissue substitute material and preparation method thereof | |
| CN109440153A (en) | Microwave-electrochemical preparation method of CuHA/GO/ dopamine composite coating | |
| CN110565144A (en) | Porous biological ceramic coating with antibacterial and bone-promoting functions and preparation method and application thereof | |
| CN105420680A (en) | Preparation method of pure titanium surface Ag/Sr co-doped TiO2 porous film | |
| CN105497990B (en) | A kind of three-dimensional porous titanium-based magnesium doping coating and preparation method thereof | |
| CN105624762B (en) | Method for preparing bioactive composite coating on surface of titanium or titanium alloy | |
| CN104001207A (en) | Medical titanium surface composite coating and preparation method thereof | |
| CN101358370A (en) | Electrochemical method for preparing hydroxylapatite granule thin coating on metallo-implantation surface | |
| CN101773412A (en) | Surface activation method of dental implant | |
| CN105565819B (en) | A kind of method and its application for adjusting silicon nitride ceramics bioactivity and bacteriostasis property |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20120919 Termination date: 20150121 |
|
| EXPY | Termination of patent right or utility model |