CN108452372A - Silk powder synchronizes the method that laser deposition prepares the titanium alloy bone implant of surface bioactive - Google Patents
Silk powder synchronizes the method that laser deposition prepares the titanium alloy bone implant of surface bioactive Download PDFInfo
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- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/06—Titanium or titanium alloys
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS 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
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/306—Other specific inorganic materials not covered by A61L27/303 - A61L27/32
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS 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
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/28—Materials for coating prostheses
- A61L27/30—Inorganic materials
- A61L27/32—Phosphorus-containing materials, e.g. apatite
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS 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
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y10/00—Processes of additive manufacturing
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- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
- C23C24/08—Coating starting from inorganic powder by application of heat or pressure and heat
- C23C24/10—Coating starting from inorganic powder by application of heat or pressure and heat with intermediate formation of a liquid phase in the layer
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- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
- C23C24/08—Coating starting from inorganic powder by application of heat or pressure and heat
- C23C24/10—Coating starting from inorganic powder by application of heat or pressure and heat with intermediate formation of a liquid phase in the layer
- C23C24/103—Coating with metallic material, i.e. metals or metal alloys, optionally comprising hard particles, e.g. oxides, carbides or nitrides
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS 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
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/18—Modification of implant surfaces in order to improve biocompatibility, cell growth, fixation of biomolecules, e.g. plasma treatment
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2420/00—Materials or methods for coatings medical devices
- A61L2420/02—Methods for coating medical devices
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2420/00—Materials or methods for coatings medical devices
- A61L2420/06—Coatings containing a mixture of two or more compounds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS 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
- A61L2430/00—Materials or treatment for tissue regeneration
- A61L2430/02—Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants
Abstract
Silk powder synchronizes the method that laser deposition prepares the titanium alloy bone implant of surface bioactive, is related to a kind of preparation method of the titanium alloy bone implant of surface bioactive.It is that existing method to be solved prepares the biological coating of titanium alloy bone implant and is easy to fall off, cannot achieve personalized customized problem.Method：One, titanium alloy wire materials are sent into laser molten pool region paraxonic by wire-feed motor, titanium alloy wire materials are as the movement in molten bath is gradually melted and is frozen into titanium alloy sedimentary again, then titanium alloy sedimentary is prepared again in first titanium alloy sedimentary, so repeat, successively prepare titanium alloy sedimentary, as titanium alloy substrate；Two, while continuing paraxonic feeding titanium alloy wire materials, it is coaxially sent into hydroxyapatite powder, hydroxyapatite titanium composite material layer is formed in the surface stack laser deposition of titanium alloy substrate, obtains the titanium alloy bone implant of surface bioactive.The present invention is used to prepare the titanium alloy bone implant of surface bioactive.
Description
Technical field
The present invention relates to a kind of preparation methods of the titanium alloy bone implant of surface bioactive.
Background technology
As bio-medical material, titanium alloy relies on its good bio-compatibility, corrosion resistance and excellent mechanicalness
Can, have in terms of the bone implants such as artificial bone holder, joint prosthesis, artificial tooth and widely applies.But pure titanium and titanium close
Gold does not have bioactivity, with tissue is only mechanical interlock after being implanted into human body, rather than reliable chemical synostosis.
In recent years, laser technology is just gradually applied to biologic medical field.For above-mentioned existing for titanium alloy medical material
Deficiency, currently used method are prepared by the method for preset hydroxyapatite (HA) powder laser deposition in titanium alloy surface
HA biological coatings, to improve the bioactivity of titanium alloy surface.But above method is confined in existing bone implant part base
Surface modification is carried out on plinth, it is difficult to meet the customized demand of personalization of user.And HA biological coatings are easy to fall off, and reduce material
The service life of material.
Invention content
The biological coating that titanium alloy bone implant is prepared the present invention is to solve existing method is easy to fall off, and cannot achieve a
The customized problem of propertyization provides a kind of silk powder and synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method.
Silk powder of the present invention synchronizes the method that laser deposition prepares the titanium alloy bone implant of surface bioactive, including following
Step：
One, bone implant matrix is prepared：
By wire-feed motor to laser molten pool region paraxonic be sent into titanium alloy wire materials, titanium alloy wire materials with molten bath movement by
It is gradually melted and is frozen into titanium alloy sedimentary again, then prepare titanium alloy deposition again in first titanium alloy sedimentary
Layer so repeats, successively prepares titanium alloy sedimentary, as titanium alloy substrate；After each layer of titanium alloy sedimentary is completed, send
The wire feed extrusion head and laser head of silk machine vertically move up, in order to successively prepare titanium alloy sedimentary；
Two, biologically active surface deposits are prepared：
While continuing paraxonic feeding titanium alloy wire materials, it is coaxially sent into hydroxyapatite (HA) powder, titanium alloy-based
The surface stack laser deposition of body forms hydroxyapatite-titanium (HA-Ti) composite layer, and the titanium for obtaining surface bioactive closes
Golden bone implant.Wherein the powder sending quantity of hydroxyapatite powder gradually increases in step 2, to realize HA volume fractions from titanium
The gradient of alloy substrate to HA-Ti composite surfaces is distributed.
Wherein technological parameter is：500~1600W of laser output power, 0.01~0.05m/min of sweep speed, laser are adopted
With positive out of focus, 2~4mm of laser beam spot diameter is protected using coaxial argon gas, and wire feeding mode is wire feed before light, wire feed rate 20-
80cm/min, deposition head inclination angle are 5-15 °, and wire feed angle is 5-20 °, powder feeding rate 100-200mg/s, powder feeding carrier gas flux 5-
10L/min, protection air-flow amount 5-10L/min.
The wherein described deposition head inclination angle is the angle of beam direction and sedimentary normal.
Further, in step 1 after first titanium alloy sedimentary is completed, when each titanium alloy sedimentary deposits
Laser power than first titanium alloy sedimentary reduce 100-300W.
The present invention synchronizes the titanium alloy bone implant that addition laser deposition prepares surface bioactive using silk powder.It is sharp first
With Laser Melting Deposition technology, titanium alloy wire materials are sent into using paraxonic and prepare bone implant matrix.Paraxonic is used to be sent into titanium later
Alloy wire, while the coaxial mode for being sent into HA powder prepares HA-Ti surface bioactive layers.
Beneficial effects of the present invention：
1, the method that the present invention uses Laser Melting Deposition, by adjusting the feeding amount of titanium alloy welding wire and HA powder, system
For titanium-based HA-Ti surface bioactive layers are gone out, the direct system of the titanium alloy bone implant part with surface bioactive is realized
It makes.
The Demand Design that different user can be directed to go out the bone implant model to match, and by adjust titanium alloy welding wire and
The feeding amount of HA powder prepares titanium alloy substrate and HA-Ti surface bioactive layers, realizes the titanium with surface bioactive
The direct manufacture of alloy bone implant part meets the customized demand of personalization of user.
2, the present invention combines the advantage of two kinds of material addition manners of powder feeding formula and wire feed formula, the weldering of addition and base material homogeneity
Silk can reduce the dilution rate of base material, and reduction cracks tendency since internal stress is excessively high, and it is heavy that the addition of silk material is conducive to increase
The area of lamination, can prepare that sedimentary is relatively thick, improve the deposition efficiency of laser deposition, and ensure successively giving birth to for sedimentary
It is long.At the same time, coaxial powder-feeding realizes distributions of the HA in laser molten pool, and HA is obtained in bone by rational technical process control
Controlled distribution in implant part.
The powder sending quantity of HA can realize the adjusting to HA volume fractions in bone implant part, HA powder sending quantities with flexible modulation
Gradually increase, can realize the increasing material manufacturing from titanium alloy substrate to the gradient components of HA-Ti composite surface layers, meet at
Divide and the manufacture of the gradient component of performance requires.Due to the gradient transition between titanium alloy substrate of HA-Ti superficial layers, avoid by
The problem of being easy to stress concentration between surface HA bioactive layers and basal body interface caused by physical property notable difference, to effectively anti-
Only surface bioactive layer falls off.HA controlled distributions in surface-active layer are obtained by rational technical process control, are obtained
Obtain the medical bone implant part with excellent mechanical performance and biological property.The average hardness of titanium alloy substrate is 345HV0.2,
And HA layer surface microhardnesses prepared by the present invention are 810HV0.2, i.e. the compound microhardness of bioceramic is the 2.35 of matrix
Times.And transitional region firmness change is gradual change under gradient components, avoids the mutation of hardness number.
3, the method for the present invention is simple, and efficiently, low cost, high degree of automation has good answer in biologic medical field
Use foreground.
Description of the drawings
Fig. 1 is the schematic diagram that titanium alloy implant is prepared using the successively superposition of wire feed formula laser deposition；Wherein 1 is laser
Head, 2 be welding wire, and 3 be protection gas, and 4 titanium alloy sedimentaries, 5 be titanium alloy substrate, and A is machine direction；
Fig. 2 is to synchronize laser deposition using silk powder to prepare titanium alloy implant surfaces HA-Ti bioactive layer schematic diagrames；Its
In 1 be laser head, 2 be welding wire, and 3 be protection gas, and 4 titanium alloy sedimentaries, 5 be titanium alloy substrate, and 6 be HA-Ti composite layers,
A is machine direction.
Specific implementation mode
Technical solution of the present invention is not limited to act specific implementation mode set forth below, further includes between each specific implementation mode
Arbitrary combination.
Specific implementation mode one：Present embodiment silk powder synchronizes the titanium alloy bone plant that laser deposition prepares surface bioactive
The method for entering body, includes the following steps：
One, bone implant matrix is prepared：
By wire-feed motor to laser molten pool region paraxonic be sent into titanium alloy wire materials, titanium alloy wire materials with molten bath movement by
It is gradually melted and is frozen into titanium alloy sedimentary again, then prepare titanium alloy deposition again in first titanium alloy sedimentary
Layer so repeats, successively prepares titanium alloy sedimentary, as titanium alloy substrate；
Two, biologically active surface deposits are prepared：
While continuing paraxonic feeding titanium alloy wire materials, it is coaxially sent into hydroxyapatite powder, in titanium alloy substrate
Surface stack laser deposition forms hydroxyapatite-titanium composite material layer, obtains the titanium alloy bone implant of surface bioactive；
Wherein the powder sending quantity of hydroxyapatite powder gradually increases in step 2；
Wherein technological parameter is：500~1600W of laser output power, 0.01~0.05m/min of sweep speed, laser are adopted
With positive out of focus, 2~4mm of laser beam spot diameter is protected using coaxial argon gas, and wire feeding mode is wire feed before light, wire feed rate 20-
80cm/min, deposition head inclination angle are 5-15 °, and wire feed angle is 5-20 °, powder feeding rate 100-200mg/s, powder feeding carrier gas flux 5-
10L/min, protection air-flow amount 5-10L/min.
The wherein described deposition head inclination angle is the angle of beam direction and sedimentary normal.
Specific implementation mode two：The present embodiment is different from the first embodiment in that：In first titanium in step 1
After alloy deposition layer is completed, laser power than first titanium alloy sedimentary when each titanium alloy sedimentary deposits reduces
100-300W.It is other same as the specific embodiment one.
Specific implementation mode three：The present embodiment is different from the first and the second embodiment in that：Speed is scanned in step 2
Degree is 0.02~0.04m/min.It is other the same as one or two specific embodiments.
Specific implementation mode four：Unlike one of present embodiment and specific implementation mode one to three：It is sent in step 2
Silk speed 40-60cm/min.It is other identical as one of specific implementation mode one to three.
Specific implementation mode five：Unlike one of present embodiment and specific implementation mode one to four：It sinks in step 2
Product head inclination angle is 10 °.It is other identical as one of specific implementation mode one to four.
Specific implementation mode six：Unlike one of present embodiment and specific implementation mode one to five：It is sent in step 2
Silk angle is 10-15 °.It is other identical as one of specific implementation mode one to five.
Specific implementation mode seven：Unlike one of present embodiment and specific implementation mode one to six：It is sent in step 2
Powder rate 100-200mg/s.It is other identical as one of specific implementation mode one to six.
Elaborate below to the embodiment of the present invention, following embodiment under based on the technical solution of the present invention into
Row is implemented, and gives detailed embodiment and specific operating process, but protection scope of the present invention is not limited to following realities
Apply example.
Embodiment 1：
Illustrate that the present embodiment, the present embodiment silk powder synchronize the titanium that laser deposition prepares surface bioactive in conjunction with Fig. 1 and Fig. 2
The method of alloy bone implant, includes the following steps：
One, bone implant matrix is prepared：
By wire-feed motor to laser molten pool region paraxonic be sent into titanium alloy wire materials, titanium alloy wire materials with molten bath movement by
It is gradually melted and is frozen into titanium alloy sedimentary again, then prepare titanium alloy deposition again in first titanium alloy sedimentary
Layer so repeats, successively prepares titanium alloy sedimentary, as titanium alloy substrate；After each layer of titanium alloy sedimentary is completed, send
The wire feed extrusion head and laser head of silk machine vertically move up, in order to successively prepare titanium alloy sedimentary；
The laser output power of first titanium alloy sedimentary is 1000W, when each titanium alloy sedimentary later deposits
Laser output power be 800W；
Two, biologically active surface deposits are prepared：
While continuing paraxonic feeding titanium alloy wire materials, it is coaxially sent into hydroxyapatite (HA) powder, titanium alloy-based
The surface stack laser deposition of body forms hydroxyapatite-titanium (HA-Ti) composite layer, and the titanium for obtaining surface bioactive closes
Golden bone implant.Wherein the powder sending quantity of hydroxyapatite powder gradually increases in step 2, and powder sending quantity range can be in 0.5g/min-
Change within the scope of 3.0g/min.To realize that HA volume fractions are distributed from titanium alloy substrate to the gradient of HA-Ti composite surfaces.
Wherein technological parameter is：0.01~0.05m/min of sweep speed, laser use positive out of focus, laser beam spot diameter 2
~4mm is protected using coaxial argon gas, and wire feeding mode is wire feed before light, and wire feed rate 60cm/min, deposition head inclination angle is 10 °, is sent
Silk angle is 10 °, powder feeding rate 150mg/s, powder feeding carrier gas flux 10L/min, protection air-flow amount 10L/min.
The wherein described deposition head inclination angle is the angle of beam direction and sedimentary normal.
The present embodiment combines the advantage of two kinds of material addition manners of powder feeding formula and wire feed formula, the weldering of addition and base material homogeneity
Silk can reduce the dilution rate of base material, and reduction cracks tendency since internal stress is excessively high, and it is heavy that the addition of silk material is conducive to increase
The area of lamination, can prepare that sedimentary is relatively thick, improve the deposition efficiency of laser deposition, and ensure successively giving birth to for sedimentary
It is long.At the same time, coaxial powder-feeding realizes distributions of the HA in laser molten pool, and HA is obtained in bone by rational technical process control
Controlled distribution in implant part.
The powder sending quantity of HA can realize the adjusting to HA volume fractions in bone implant part, HA powder sending quantities with flexible modulation
Gradually increase, can realize the increasing material manufacturing from titanium alloy substrate to the gradient components of HA-Ti composite surface layers, meet at
Divide and the manufacture of the gradient component of performance requires.Due to the gradient transition between titanium alloy substrate of HA-Ti superficial layers, avoid by
The problem of being easy to stress concentration between surface HA bioactive layers and basal body interface caused by physical property notable difference, to effectively anti-
Only surface bioactive layer falls off.HA controlled distributions in surface-active layer are obtained by rational technical process control, are obtained
Obtain the medical bone implant part with excellent mechanical performance and biological property.
The average hardness of titanium alloy substrate is 345HV0.2, and HA layer surfaces microhardness manufactured in the present embodiment is
810HV0.2, i.e. the compound microhardness of bioceramic is 2.35 times of matrix.And transitional region firmness change is under gradient components
Gradual change avoids the mutation of hardness number.
Claims (7)
1. silk powder synchronizes the method that laser deposition prepares the titanium alloy bone implant of surface bioactive, it is characterised in that this method
Include the following steps：
One, bone implant matrix is prepared：
Be sent into titanium alloy wire materials to laser molten pool region paraxonic by wire-feed motor, titanium alloy wire materials with molten bath the gradual quilt of movement
It melts and is frozen into titanium alloy sedimentary again, then prepare titanium alloy sedimentary again in first titanium alloy sedimentary,
It so repeats, successively prepares titanium alloy sedimentary, as titanium alloy substrate；
Two, biologically active surface deposits are prepared：
While continuing paraxonic feeding titanium alloy wire materials, it is coaxially sent into hydroxyapatite powder, on the surface of titanium alloy substrate
Lamination laser deposition forms hydroxyapatite-titanium composite material layer, obtains the titanium alloy bone implant of surface bioactive；Wherein
The powder sending quantity of hydroxyapatite powder gradually increases in step 2；
Wherein technological parameter is：500~1600W of laser output power, 0.01~0.05m/min of sweep speed, laser is using just
Defocus, 2~4mm of laser beam spot diameter are protected using coaxial argon gas, and wire feeding mode is wire feed before light, wire feed rate 20-
80cm/min, deposition head inclination angle are 5-15 °, and wire feed angle is 5-20 °, powder feeding rate 100-200mg/s, powder feeding carrier gas flux 5-
10L/min, protection air-flow amount 5-10L/min.
2. silk powder according to claim 1 synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method, it is characterised in that：In step 1 after first titanium alloy sedimentary is completed, swashing when each titanium alloy sedimentary deposits
Luminous power than first titanium alloy sedimentary reduces 100-300W.
3. silk powder according to claim 1 or 2 synchronizes the titanium alloy bone implant that laser deposition prepares surface bioactive
Method, it is characterised in that：Sweep speed is 0.02~0.04m/min in step 2.
4. silk powder according to claim 3 synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method, it is characterised in that：Wire feed rate 40-60cm/min in step 2.
5. silk powder according to claim 4 synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method, it is characterised in that：Deposition head inclination angle is 10 ° in step 2.
6. silk powder according to claim 5 synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method, it is characterised in that：Wire feed angle is 10-15 ° in step 2.
7. silk powder according to claim 6 synchronizes the side that laser deposition prepares the titanium alloy bone implant of surface bioactive
Method, it is characterised in that：Powder feeding rate 100-200mg/s in step 2.
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111112609A (en) * | 2019-12-20 | 2020-05-08 | 西安交通大学 | Micro-scale RE2O3Titanium alloy wire filling additive manufacturing method for particle multistage refining microstructure |
| CN111151757A (en) * | 2020-02-21 | 2020-05-15 | 上海理工大学 | Composite electron beam additive manufacturing equipment and process |
| CN111420118A (en) * | 2020-03-05 | 2020-07-17 | 重庆大学 | Titanium-based active bone implant with ROS response and preparation method thereof |
| CN112743244A (en) * | 2021-01-05 | 2021-05-04 | 兰州理工大学 | Laser coaxial powder feeding and welding wire coupling welding device and method |
| CN114074232A (en) * | 2020-08-21 | 2022-02-22 | 拓乾自动化装备(上海)有限公司 | Multifunctional laser processing head |
| KR102386092B1 (en) * | 2021-01-18 | 2022-04-14 | 창원대학교 산학협력단 | 3D printer capable of laminating powder or wire materials |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101249279A (en) * | 2008-03-19 | 2008-08-27 | 中国人民解放军第四军医大学 | Method using laser quick forming producing HA/Ti gradient biological activity material |
| CN104313571A (en) * | 2014-11-06 | 2015-01-28 | 哈尔滨工业大学 | Method for preparing aluminum matrix composite member by synchronous feeding and laser deposition of silk powder |
| CN105170979A (en) * | 2015-11-03 | 2015-12-23 | 哈尔滨工业大学 | Side-shaft powder-feeding nozzle for laser additive manufacturing |
-
2018
- 2018-05-22 CN CN201810497431.1A patent/CN108452372B/en active Active
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101249279A (en) * | 2008-03-19 | 2008-08-27 | 中国人民解放军第四军医大学 | Method using laser quick forming producing HA/Ti gradient biological activity material |
| CN104313571A (en) * | 2014-11-06 | 2015-01-28 | 哈尔滨工业大学 | Method for preparing aluminum matrix composite member by synchronous feeding and laser deposition of silk powder |
| CN105170979A (en) * | 2015-11-03 | 2015-12-23 | 哈尔滨工业大学 | Side-shaft powder-feeding nozzle for laser additive manufacturing |
Cited By (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111112609A (en) * | 2019-12-20 | 2020-05-08 | 西安交通大学 | Micro-scale RE2O3Titanium alloy wire filling additive manufacturing method for particle multistage refining microstructure |
| CN111151757A (en) * | 2020-02-21 | 2020-05-15 | 上海理工大学 | Composite electron beam additive manufacturing equipment and process |
| CN111420118A (en) * | 2020-03-05 | 2020-07-17 | 重庆大学 | Titanium-based active bone implant with ROS response and preparation method thereof |
| CN111420118B (en) * | 2020-03-05 | 2022-05-17 | 重庆大学 | Titanium-based active bone implant with ROS response and preparation method thereof |
| CN114074232A (en) * | 2020-08-21 | 2022-02-22 | 拓乾自动化装备(上海)有限公司 | Multifunctional laser processing head |
| CN112743244A (en) * | 2021-01-05 | 2021-05-04 | 兰州理工大学 | Laser coaxial powder feeding and welding wire coupling welding device and method |
| KR102386092B1 (en) * | 2021-01-18 | 2022-04-14 | 창원대학교 산학협력단 | 3D printer capable of laminating powder or wire materials |
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