CN115475278A - Degradable zinc-cerium alloy bone grafting bed device for rear of vertebral body - Google Patents
Degradable zinc-cerium alloy bone grafting bed device for rear of vertebral body Download PDFInfo
- Publication number
- CN115475278A CN115475278A CN202210933903.XA CN202210933903A CN115475278A CN 115475278 A CN115475278 A CN 115475278A CN 202210933903 A CN202210933903 A CN 202210933903A CN 115475278 A CN115475278 A CN 115475278A
- Authority
- CN
- China
- Prior art keywords
- zinc
- bone grafting
- cerium
- bed device
- powder
- 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
- 210000000988 bone and bone Anatomy 0.000 title claims abstract description 85
- UFNRFBFHJJPDNF-UHFFFAOYSA-N [Zn].[Ce] Chemical compound [Zn].[Ce] UFNRFBFHJJPDNF-UHFFFAOYSA-N 0.000 title claims abstract description 73
- 229910000636 Ce alloy Inorganic materials 0.000 title claims abstract description 72
- 239000000843 powder Substances 0.000 claims abstract description 54
- HCHKCACWOHOZIP-UHFFFAOYSA-N Zinc Chemical compound [Zn] HCHKCACWOHOZIP-UHFFFAOYSA-N 0.000 claims abstract description 16
- GWXLDORMOJMVQZ-UHFFFAOYSA-N cerium Chemical compound [Ce] GWXLDORMOJMVQZ-UHFFFAOYSA-N 0.000 claims abstract description 16
- 229910052684 Cerium Inorganic materials 0.000 claims abstract description 15
- 229910052725 zinc Inorganic materials 0.000 claims abstract description 10
- 239000011701 zinc Substances 0.000 claims abstract description 10
- 239000010935 stainless steel Substances 0.000 claims abstract description 9
- 229910001220 stainless steel Inorganic materials 0.000 claims abstract description 9
- 238000002844 melting Methods 0.000 claims abstract description 6
- 230000008018 melting Effects 0.000 claims abstract description 6
- 238000005488 sandblasting Methods 0.000 claims description 36
- 238000000034 method Methods 0.000 claims description 34
- 230000008569 process Effects 0.000 claims description 26
- 239000002245 particle Substances 0.000 claims description 22
- 238000004140 cleaning Methods 0.000 claims description 17
- 238000005422 blasting Methods 0.000 claims description 12
- 229910052593 corundum Inorganic materials 0.000 claims description 12
- 239000010431 corundum Substances 0.000 claims description 12
- 239000011521 glass Substances 0.000 claims description 12
- 239000004576 sand Substances 0.000 claims description 12
- 238000005507 spraying Methods 0.000 claims description 12
- 238000004381 surface treatment Methods 0.000 claims description 12
- 238000000498 ball milling Methods 0.000 claims description 11
- 239000010410 layer Substances 0.000 claims description 9
- 238000005245 sintering Methods 0.000 claims description 9
- CSCPPACGZOOCGX-UHFFFAOYSA-N Acetone Chemical compound CC(C)=O CSCPPACGZOOCGX-UHFFFAOYSA-N 0.000 claims description 8
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 claims description 8
- 239000006187 pill Substances 0.000 claims description 8
- 238000002360 preparation method Methods 0.000 claims description 6
- 229910001297 Zn alloy Inorganic materials 0.000 claims description 5
- XKRFYHLGVUSROY-UHFFFAOYSA-N Argon Chemical compound [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 claims description 4
- LFQSCWFLJHTTHZ-UHFFFAOYSA-N Ethanol Chemical compound CCO LFQSCWFLJHTTHZ-UHFFFAOYSA-N 0.000 claims description 4
- 239000003082 abrasive agent Substances 0.000 claims description 4
- 238000001035 drying Methods 0.000 claims description 4
- 238000009499 grossing Methods 0.000 claims description 4
- 239000000463 material Substances 0.000 claims description 4
- 238000002156 mixing Methods 0.000 claims description 4
- 229910052757 nitrogen Inorganic materials 0.000 claims description 4
- 238000004506 ultrasonic cleaning Methods 0.000 claims description 4
- 239000012300 argon atmosphere Substances 0.000 claims description 3
- 238000000227 grinding Methods 0.000 claims description 3
- 239000002356 single layer Substances 0.000 claims description 3
- 238000005303 weighing Methods 0.000 claims description 3
- 229910052786 argon Inorganic materials 0.000 claims description 2
- 239000007789 gas Substances 0.000 claims description 2
- 238000000713 high-energy ball milling Methods 0.000 claims description 2
- 230000000844 anti-bacterial effect Effects 0.000 abstract description 11
- 241000894006 Bacteria Species 0.000 abstract description 6
- 208000035143 Bacterial infection Diseases 0.000 abstract description 4
- 206010061218 Inflammation Diseases 0.000 abstract description 4
- 208000022362 bacterial infectious disease Diseases 0.000 abstract description 4
- 230000004054 inflammatory process Effects 0.000 abstract description 4
- 229910001069 Ti alloy Inorganic materials 0.000 abstract description 3
- 230000015556 catabolic process Effects 0.000 abstract description 3
- 238000006731 degradation reaction Methods 0.000 abstract description 3
- 239000007943 implant Substances 0.000 abstract description 3
- 238000006479 redox reaction Methods 0.000 abstract description 3
- 230000008439 repair process Effects 0.000 abstract description 3
- 229910000531 Co alloy Inorganic materials 0.000 abstract description 2
- QMTNJXLAAQEFPY-UHFFFAOYSA-N [Zn].[Fe].[Ce] Chemical compound [Zn].[Fe].[Ce] QMTNJXLAAQEFPY-UHFFFAOYSA-N 0.000 abstract description 2
- -1 cerium ions Chemical class 0.000 abstract description 2
- 230000008034 disappearance Effects 0.000 abstract 1
- 230000000694 effects Effects 0.000 abstract 1
- 238000012360 testing method Methods 0.000 description 13
- 229910052751 metal Inorganic materials 0.000 description 7
- 239000002184 metal Substances 0.000 description 7
- 230000005764 inhibitory process Effects 0.000 description 6
- 239000000956 alloy Substances 0.000 description 5
- 230000003385 bacteriostatic effect Effects 0.000 description 5
- 230000006378 damage Effects 0.000 description 5
- 230000004927 fusion Effects 0.000 description 5
- 230000006837 decompression Effects 0.000 description 4
- 210000001519 tissue Anatomy 0.000 description 4
- 239000007857 degradation product Substances 0.000 description 3
- 210000001951 dura mater Anatomy 0.000 description 3
- 125000001475 halogen functional group Chemical group 0.000 description 3
- 238000002684 laminectomy Methods 0.000 description 3
- 208000027418 Wounds and injury Diseases 0.000 description 2
- 230000009471 action Effects 0.000 description 2
- 229910045601 alloy Inorganic materials 0.000 description 2
- 201000010099 disease Diseases 0.000 description 2
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 2
- 208000014674 injury Diseases 0.000 description 2
- 231100000956 nontoxicity Toxicity 0.000 description 2
- 230000002980 postoperative effect Effects 0.000 description 2
- 238000012113 quantitative test Methods 0.000 description 2
- 210000000278 spinal cord Anatomy 0.000 description 2
- 238000009864 tensile test Methods 0.000 description 2
- 238000010998 test method Methods 0.000 description 2
- 206010013886 Dysaesthesia Diseases 0.000 description 1
- 206010050296 Intervertebral disc protrusion Diseases 0.000 description 1
- 206010040007 Sense of oppression Diseases 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- 238000000149 argon plasma sintering Methods 0.000 description 1
- 239000002775 capsule Substances 0.000 description 1
- 210000000845 cartilage Anatomy 0.000 description 1
- 238000012512 characterization method Methods 0.000 description 1
- 230000000052 comparative effect Effects 0.000 description 1
- 230000008602 contraction Effects 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 230000005786 degenerative changes Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 238000011038 discontinuous diafiltration by volume reduction Methods 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 206010025005 lumbar spinal stenosis Diseases 0.000 description 1
- 239000012567 medical material Substances 0.000 description 1
- 239000007769 metal material Substances 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 231100000252 nontoxic Toxicity 0.000 description 1
- 230000003000 nontoxic effect Effects 0.000 description 1
- 230000011164 ossification Effects 0.000 description 1
- 208000035824 paresthesia Diseases 0.000 description 1
- 229910052761 rare earth metal Inorganic materials 0.000 description 1
- 150000002910 rare earth metals Chemical class 0.000 description 1
- 210000000273 spinal nerve root Anatomy 0.000 description 1
- 208000005198 spinal stenosis Diseases 0.000 description 1
- 238000006467 substitution reaction Methods 0.000 description 1
- 208000024891 symptom Diseases 0.000 description 1
- 230000001988 toxicity Effects 0.000 description 1
- 231100000419 toxicity Toxicity 0.000 description 1
Images
Classifications
-
- 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
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/047—Other specific metals or alloys not covered by A61L27/042 - A61L27/045 or A61L27/06
-
- 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
-
- 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
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F1/00—Metallic powder; Treatment of metallic powder, e.g. to facilitate working or to improve properties
- B22F1/09—Mixtures of metallic powders
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/20—Direct sintering or melting
- B22F10/28—Powder bed fusion, e.g. selective laser melting [SLM] or electron beam melting [EBM]
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/30—Process control
- B22F10/38—Process control to achieve specific product aspects, e.g. surface smoothness, density, porosity or hollow structures
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/60—Treatment of workpieces or articles after build-up
- B22F10/66—Treatment of workpieces or articles after build-up by mechanical means
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F9/00—Making metallic powder or suspensions thereof
- B22F9/02—Making metallic powder or suspensions thereof using physical processes
- B22F9/04—Making metallic powder or suspensions thereof using physical processes starting from solid material, e.g. by crushing, grinding or milling
-
- 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
-
- 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
- B33Y40/00—Auxiliary operations or equipment, e.g. for material handling
- B33Y40/20—Post-treatment, e.g. curing, coating or polishing
-
- 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
- B33Y70/00—Materials specially adapted for additive manufacturing
-
- 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
- B33Y80/00—Products made by additive manufacturing
-
- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C18/00—Alloys based on zinc
-
- 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
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/10—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing inorganic materials
- A61L2300/102—Metals or metal compounds, e.g. salts such as bicarbonates, carbonates, oxides, zeolites, silicates
-
- 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
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
- A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
-
- 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
- A61L2430/38—Materials or treatment for tissue regeneration for reconstruction of the spine, vertebrae or intervertebral discs
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F9/00—Making metallic powder or suspensions thereof
- B22F9/02—Making metallic powder or suspensions thereof using physical processes
- B22F9/04—Making metallic powder or suspensions thereof using physical processes starting from solid material, e.g. by crushing, grinding or milling
- B22F2009/043—Making metallic powder or suspensions thereof using physical processes starting from solid material, e.g. by crushing, grinding or milling by ball milling
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
- Y02P10/00—Technologies related to metal processing
- Y02P10/25—Process efficiency
Landscapes
- Chemical & Material Sciences (AREA)
- Engineering & Computer Science (AREA)
- Health & Medical Sciences (AREA)
- Materials Engineering (AREA)
- Manufacturing & Machinery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Medicinal Chemistry (AREA)
- Transplantation (AREA)
- Epidemiology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Dermatology (AREA)
- Physics & Mathematics (AREA)
- Molecular Biology (AREA)
- Plasma & Fusion (AREA)
- Biomedical Technology (AREA)
- Inorganic Chemistry (AREA)
- Automation & Control Theory (AREA)
- Mechanical Engineering (AREA)
- Metallurgy (AREA)
- Organic Chemistry (AREA)
- Materials For Medical Uses (AREA)
Abstract
The invention relates to a degradable zinc-cerium alloy bone grafting bed device for the back of a vertebral body, wherein the degradable zinc-cerium alloy bone grafting bed device comprises a net-shaped main body structure and fixing wings at two sides of the net-shaped main body, the degradable zinc-cerium alloy bone grafting bed device is formed by melting degradable zinc-cerium alloy powder through a laser powder bed, and the iron-zinc-cerium alloy powder comprises 1-3 wt% of cerium and 97-99 wt% of zinc. Degradable zinc cerium alloy bone grafting bed device implant can be at internal natural degradation, can follow internal disappearance after accomplishing the repair effect, has avoided implants such as traditional titanium alloy, cobalt alloy, stainless steel to need the drawback that the secondary operation takes out, degradable zinc cerium alloy bone grafting bed device has good antibacterial property. During service, cerium ions released by degradation can kill bacteria through redox reaction, thereby avoiding inflammatory reaction caused by bacterial infection.
Description
Technical Field
The invention relates to the technical field of medical materials, in particular to a degradable zinc-cerium alloy bone grafting bed device for the back of a vertebral body.
Background
The lumbar disc herniation is one of the clinical common lumbar diseases, which is characterized in that after degenerative changes of various parts of the lumbar disc (nucleus pulposus, annulus fibrosus and cartilage plates) occur to different degrees, under the action of external factors, the annulus fibrosus is ruptured, the nucleus pulposus protrudes from the ruptured part, the contraction and volume reduction of various radial lines of the vertebral canal and the lateral crypt are caused, the dural sac, the spinal cord or nerve roots are pressed to cause injury, and finally, a series of clinical symptoms such as pain, soreness and dysesthesia are caused to the waist and legs. To effectively eliminate the disease, a surgical approach of laminectomy for spinal decompression is commonly used. Because of the complex physiological structure of spinal cord and spinal column, the intervertebral discs are removed outside or inside the dura mater after the spinal canal decompression operation is removed through the vertebral plate, so that the lumbar vertebrae are merged. However, complications such as instability of lumbar vertebrae and lumbar spinal stenosis occur after the combination, which requires spinal fusion.
Spinal fusion usually adopts bone grafting fusion between transverse processes on the outer side of the spine to repair bone defects. Because the vertebral column after the laminectomy does not have the back column to support, this kind of transverse process bone grafting can not fully inlay the pressure and pack, causes the bone grafting piece to fall into the canalis spinalis and causes the new hard oppression of nervous tissue, and this transverse process bone grafting can not provide effectual mechanics simultaneously, probably causes the internal fixation fracture of postoperative to become flexible and nervous tissue is pressurized and damaged once more, finally leads to postoperative rehabilitation to fail. It is therefore of great importance to use an effective and biomechanically desirable bone graft fusion following laminectomy spinal decompression. Good bone grafting conditions are often required to obtain reliable bone grafting fusion: firstly, the bone grafting bed can provide enough volume and mechanical strength support, so that the transplanted bone is fully embedded, compacted and compacted to achieve the effective stability of the spine; secondly, enough clearance is reserved between the bone grafting bed and the dura mater sac to prevent the dura mater sac from adhering to surrounding tissues; thirdly, the bone grafting bed has good biocompatibility, can not generate toxicity to surrounding tissues, and can fully play the roles of bone induction, bone conduction and osteogenesis of the transplanted bone.
At present, the bone grafting bed is mainly made of materials such as non-degradable stainless steel, titanium alloy or cobalt alloy, however, the bone grafting bed implant made of the non-degradable materials exists as foreign matters for a long time, and needs to be taken out through a secondary operation after the completion of service, thereby causing secondary damage to patients. More importantly, the local vicinity of the bone grafting bed may cause inflammatory reaction due to bacterial infection, resulting in failure of bone repair. Therefore, the bone grafting bed device which can be naturally degraded after being implanted, has no toxicity of degradation products and has good antibacterial effect is sought, and the problem which needs to be solved urgently after the decompression operation of the vertebral canal is guaranteed.
Disclosure of Invention
An object of the present invention is to solve at least the above problems and/or disadvantages and to provide at least the advantages described hereinafter.
The degradable zinc-cerium alloy bone grafting bed device is characterized by comprising a net-shaped main body structure and fixing wings on two sides of the net-shaped main body, wherein the degradable zinc-cerium alloy bone grafting bed device is formed by melting degradable zinc-cerium alloy powder through a laser powder bed, and the iron-zinc-cerium alloy powder comprises 1-3 wt% of cerium and 97-99 wt% of zinc.
A preparation method of the degradable zinc-cerium alloy bone grafting bed device for the back of a vertebral body comprises the following steps:
step one, constructing a three-dimensional bone grafting bed model through 3D modeling;
mixing zinc cerium powder through a high-energy ball milling process to obtain degradable zinc cerium alloy powder;
and step three, printing and sintering the three-dimensional bone grafting bed model according to the laser selection sintering process to form the degradable cerium-zinc alloy bone grafting bed device.
Preferably, in the second step, the zinc-cerium alloy is prepared by: weighing 1-3 parts of cerium powder and 97-99 parts of zinc powder by mass, taking a stainless steel ball mill as a mill, and uniformly mixing in an argon atmosphere by a planetary ball mill at the ball milling speed of 150rpm/min for 2-3 h to obtain the degradable zinc-cerium alloy powder.
Preferably, the continuous ball milling is stopped for 15min every 30min, then the high-energy ball mill is reversed for 30min, and after the ball milling is completed and the ball milling tank body is completely cooled, the zinc-cerium alloy powder is taken out from the vacuum glove box.
Preferably, the ball-to-material ratio between the stainless steel grinding ball and the zinc-cerium premixed powder is 10:1.
preferably, the particle diameter of the zinc powder is 17-45 μm, and the purity is 99.9%; the particle size of the cerium powder is 1-5 mu m, and the purity is 99.9%; the purity of the argon gas is 99.999%.
Preferably, wherein the laser selective sintering process comprises: laying zinc-cerium alloy powder in a melting forming system of a laser powder bed, and printing and sintering layer by layer to form a degradable cerium/zinc alloy bone grafting bed device according to a built three-dimensional model, wherein an alternate scanning strategy is adopted, namely the scanning direction is rotated by 90 degrees compared with the previous layer; the laser scanning power is 45-55W, the scanning speed is 270-320 mm/s, and the thickness of the single-layer powder is 40-60 mu m.
Preferably, the convex surface of the net-shaped main body and the outer surface of the fixing wings of the degradable zinc cerium alloy bone grafting bed device are frosted surfaces, the concave surface of the net-shaped main body and the inner surface of the fixing wings are smooth surfaces, and the surface treatment step of the degradable zinc cerium alloy bone grafting bed device is as follows:
firstly, carrying out primary surface treatment on the whole bone grafting bed device by using a sand blasting process, wherein the sand blasting adopts corundum sand with the powder particle size of 80 meshes as an abrasive, the sand blasting distance is 10cm, the sand blasting pressure is 0.6-0.8 MPa, the spraying time is 1-1.5 min, and the coverage rate is more than 100%;
step two, smoothing the concave surface of the net-shaped main body and the inner surface of the fixed wing of the bone grafting bed device by utilizing a shot blasting process, wherein the shot blasting adopts glass shots with the powder particle size of 180-220 meshes as abrasive materials, the shot blasting distance is 10-15 cm, the shot blasting pressure is 0.5-0.8 MPa, the spraying time is 2-3 min, and the coverage rate is more than 100 percent;
thirdly, performing frosting treatment on the convex surface of the net-shaped main body of the bone grafting bed device and the outer surface of the fixed wing by using a sand blasting process, wherein the sand blasting process adopts corundum sand with the powder particle size of 24-80 meshes and glass pill mixed abrasive with the powder particle size of 180-220 meshes, and the proportion of the corundum sand to the glass pill is 4:1, the sand blasting distance is 10-15 cm, the sand blasting pressure is 3.0MPa, the spraying time is 0.5-1 min, and the coverage rate is more than 100%;
step four, cleaning the bone grafting bed device obtained in the step three: and cleaning for 2-3 times by using acetone and cleaning for 3-4 times by using absolute ethyl alcohol with the aid of an ultrasonic cleaning machine, wherein the cleaning time is about 10min each time, and drying by using nitrogen after cleaning.
The invention provides a degradable zinc-cerium alloy bone grafting bed device, which has the following action principle:
the bone grafting bed device is prepared by using a zinc-cerium alloy material. As a biomedical metal material, the zinc metal has natural degradability, the degradation product has no toxicity, can be absorbed by human bodies, has good biocompatibility, cannot cause secondary damage to the human bodies, and the alloy element rare earth cerium can generate good antibacterial effect through oxidation-reduction reaction. The bone grafting bed device prepared from the zinc-cerium alloy material has good biocompatibility, can be naturally degraded in a human body after being implanted into the human body, cannot cause secondary damage to the human body, and has a good antibacterial effect, so that inflammatory reaction caused by bacterial infection is avoided.
Compared with the prior art, the preparation method of the degradable zinc-cerium alloy bone grafting bed device has the following advantages:
(1) Compared with devices made of non-degradable alloys such as titanium alloy, stainless steel and the like, the device made of the degradable zinc-cerium alloy material can be naturally degraded, degradation products are non-toxic and can be absorbed by a human body, and secondary operation injury caused by the fact that the non-degradable bone grafting bed device is implanted is avoided.
(2) The degradable zinc-cerium alloy bone graft bed device has good antibacterial performance. During service, cerium ions released by degradation can kill bacteria through redox reaction, thereby avoiding inflammatory reaction caused by bacterial infection.
(3) In the structural design of the degradable zinc-cerium alloy bone graft bed device, the net-shaped main body of the device adopts the smooth concave surface to be in contact with the hard film capsule, so that the adhesion between the net-shaped main body and the device can be avoided, and the convex surface of the net-shaped main body adopts the frosted structure, so that the device is convenient to combine with a transplanted bone to form an integrated structure.
Description of the drawings:
FIG. 1 is a test chart of antibacterial performance in example 1, in which a is a chart of a zone of inhibition by the halo method, b is a chart comparing widths of zones of inhibition in the zone a, c is a test chart of inhibition of bacteria, and d is a chart comparing results of inhibition of bacteria in the zone c;
fig. 2 is a bone graft bed device provided by the present invention.
The specific implementation mode is as follows:
to facilitate an understanding of the invention, the invention will now be described more fully with reference to the accompanying drawings. Preferred embodiments of the present invention are shown in the drawings. This invention may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided so that this disclosure will be thorough and complete.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. The terminology used in the description of the invention herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items.
The invention is described in more detail below with reference to specific examples.
Example 1:
(1) The three-dimensional model of the bone grafting bed device is constructed by utilizing 3D modeling, the bone grafting bed device comprises a net-shaped main body 1 and fixing wings 2 on two sides of the net-shaped main body, a plurality of net-shaped circular holes 3 are distributed on the net-shaped main body 1, the fixing wings 2 are provided with a plurality of screw holes 4 which are symmetrically distributed left and right, the net-shaped main body part of the device is designed into an arc net-shaped structure, and the angle of a central angle is adjusted according to the curvature of a vertebral canal behind a vertebral body of a patient.
(2) Weighing 0.2g of cerium powder with the particle size of 1-5 mu m and 9.8g of zinc powder with the particle size of 17-45 mu m and the purity of 99.9 percent by using an electronic balance; adding the two powders into a hard stainless steel ball milling tank, adding 100g of stainless steel grinding balls with the diameter of 3mm, and carrying out ball milling for 2 hours at the rotating speed of 150rpm/min in a planetary ball milling mode under the protection of 99.999% high-purity argon atmosphere. And after the tank body is completely cooled, taking out the zinc-cerium alloy powder in a vacuum glove box.
(3) Laying zinc-cerium alloy powder in a melting forming system of a laser powder bed, and printing and sintering layer by layer to form a degradable cerium/zinc alloy bone grafting bed device according to a built three-dimensional model, wherein an alternate scanning strategy is adopted, namely the scanning direction is rotated by 90 degrees compared with the previous layer; the laser scanning power is 50W, the scanning speed is 300mm/s, and the thickness of single-layer powder is 50 mu m.
In example 1, the prepared degradable zinc-cerium alloy bone grafting bed device is subjected to performance characterization;
(a) Qualitative and quantitative tests are carried out on the antibacterial property of a zinc-cerium alloy sample, qualitative tests are carried out on the zinc-cerium alloy by using a bacteriostatic ring test method (halo method), the test result is shown in figure 1, the width of the bacteriostatic ring of the zinc-cerium alloy is larger than that of a zinc metal bacteriostatic ring, and the zinc-cerium alloy has obvious antibacterial ability; the antibacterial property of the zinc-cerium alloy is quantitatively tested, and the bacteria inhibition rate is higher than 80 percent and is obviously superior to that of zinc metal.
(b) And (4) preparing a tensile test sample strip by the laser sintering process which is the same as that in the step (3), and testing the tensile mechanical property of the test sample strip to obtain the tensile test sample strip with the ultimate tensile strength of 247.4MPa, the yield strength of 180.6MPa and the tensile deformation of 7.6 percent, wherein the ultimate tensile strength, the yield strength and the tensile deformation are all improved to a certain extent compared with zinc metal.
Example 2:
(1) The remaining parameters were the same as those in example 1, and therefore, details were not repeated, except that 0.1g of cerium powder and 9.9g of zinc powder were weighed using an electronic balance.
(a) Mechanical property tests show that the ultimate tensile strength of a zinc-cerium alloy sample is 194.1MPa, the yield strength is 138.5MPa, and the tensile deformation is 6 percent, so that the zinc-cerium alloy sample is improved to a certain extent compared with zinc metal.
Example 3:
the remaining parameters are the same as those in embodiment 1, and thus are not described again. Except that 0.3g of cerium powder and 9.7g of cerium powder were weighed using an electronic balance.
(a) Mechanical property tests show that the ultimate tensile strength of a zinc-cerium alloy sample is 230.3MPa, the yield strength is 188.2MPa, and the tensile deformation is 6.8%, which are improved to a certain extent compared with zinc metal.
Example 4:
the remaining parameters are the same as those in embodiment 1, and thus are not described again. The difference lies in that the surface treatment is carried out on the bone grafting bed device, and the steps are as follows:
firstly, carrying out primary surface treatment on the whole bone grafting bed device by using a sand blasting process, wherein the sand blasting adopts corundum sand with the powder particle size of 80 meshes as an abrasive, the sand blasting distance is 10cm, the sand blasting pressure is 0.6MPa, the spraying time is 1min, and the coverage rate is more than 100%;
step two, smoothing the concave surface of the net-shaped main body of the bone grafting bed device and the inner surface of the fixed wing by utilizing a shot blasting process, wherein the shot blasting adopts glass shots with the powder particle size of 220 meshes as abrasive materials, the shot blasting distance is 10cm, the shot blasting pressure is 0.8MPa, the spraying time is 2min, and the coverage rate is more than 100%;
thirdly, carrying out frosting treatment on the convex surface of the net-shaped main body of the bone grafting bed device and the outer surface of the fixed wing by using a sand blasting process, wherein the sand blasting process adopts corundum sand with the powder particle size of 80 meshes and glass pill mixed abrasive with the powder particle size of 220 meshes, and the proportion of the corundum sand to the glass pill is 4:1, the sand blasting distance is 15cm, the sand blasting pressure is 3.0MPa, the spraying time is 1min, and the coverage rate is more than 100%;
step four, cleaning the bone grafting bed device obtained in the step three: and cleaning for 3 times by using acetone and 3 times by using absolute ethyl alcohol with the aid of an ultrasonic cleaning machine, wherein the cleaning time is about 10min each time, and drying by using nitrogen after cleaning.
(a) The same surface treatment is carried out on the sample strip, and the ultimate compressive strength of the zinc-cerium alloy sample is 283.4MPa and the yield strength is 202.8MPa through mechanical property tests, and the ultimate tensile strength of the zinc-cerium alloy sample is improved to a certain extent compared with the zinc-cerium alloy sample which is not subjected to surface treatment.
Example 5:
the remaining parameters are the same as those in embodiment 2, and thus are not described again. Except that the bone graft bed device obtained was subjected to surface treatment. The method comprises the following steps: carrying out surface treatment on the obtained bone grafting bed device, and comprising the following steps:
firstly, carrying out primary surface treatment on the whole bone grafting bed device by using a sand blasting process, wherein the sand blasting adopts corundum sand with the powder particle size of 80 meshes as an abrasive, the sand blasting distance is 15cm, the sand blasting pressure is 0.8MPa, the spraying time is 1.5min, and the coverage rate is more than 100%;
step two, smoothing the inner surface of the bone grafting bed device by utilizing a shot blasting process, wherein the shot blasting adopts glass shots with the powder particle size of 180 meshes as abrasive materials, the sand blasting distance is 15cm, the sand blasting pressure is 0.8MPa, the spraying time is 3min, and the coverage rate is more than 100%;
thirdly, the outer surface of the bone grafting bed device is subjected to rough treatment by using a sand blasting process, wherein the sand blasting process adopts corundum sand with the powder particle size of 24 meshes and glass pill mixed abrasive with the powder particle size of 180 meshes, and the ratio of the corundum sand to the glass pill is 4:1, the sand blasting distance is 10cm, the sand blasting pressure is 3.0MPa, the spraying time is 0.5min, and the coverage rate is more than 100 percent;
step four, cleaning the bone grafting bed device obtained in the step three: cleaning with acetone for 2 times and absolute ethyl alcohol for 4 times with the aid of an ultrasonic cleaning machine, wherein the cleaning time is about 10min each time, and drying with nitrogen after cleaning.
(a) Through mechanical property tests, the ultimate tensile strength of the zinc-cerium alloy sample is 217.6MPa, the yield strength is 157.3MPa, and the ultimate tensile strength of the zinc-cerium alloy sample is improved to a certain extent compared with that of the zinc-cerium alloy sample which is not subjected to surface treatment.
Comparative example 1:
the remaining experimental conditions were the same as in example 1 except that the cerium content was 0wt%.
(a) Qualitative and quantitative tests are carried out on the antibacterial property of the zinc-cerium alloy, qualitative tests are carried out on zinc metal by using a bacteriostatic ring test method (halo method), the test result is shown in figure 1, and the bacteriostatic ring of the zinc-cerium alloy is narrower and obviously smaller than that of the zinc-cerium alloy; the antibacterial property of the zinc-cerium alloy is quantitatively tested, and the bacteria inhibition rate is less than 40 percent
(b) Through mechanical property tests, the ultimate tensile strength of a zinc-cerium alloy sample is 103.7MPa, the yield strength is 79.9MPa, and the tensile deformation is 5.1%.
Finally, it should be noted that: although the present invention has been described in detail with reference to the foregoing embodiments, it should be understood by those skilled in the art that the following descriptions are only illustrative and not restrictive, and that the scope of the present invention is not limited to the above embodiments: any person skilled in the art can modify or easily conceive the technical solutions described in the foregoing embodiments or equivalent substitutes for some technical features within the technical scope of the present disclosure; such modifications, changes or substitutions do not depart from the spirit and scope of the embodiments of the present invention, and they should be construed as being included therein. Therefore, the protection scope of the present invention shall be subject to the protection scope.
Claims (8)
1. The degradable zinc-cerium alloy bone grafting bed device for the back of the vertebral body is characterized by comprising a net-shaped main body structure and fixing wings on two sides of the net-shaped main body, wherein degradable zinc-cerium alloy bone grafting bed device is formed by melting degradable zinc-cerium alloy powder through a laser powder bed, and the zinc-cerium alloy powder comprises 1-3 wt% of cerium and 97-99 wt% of zinc.
2. The preparation method of the degradable zinc cerium alloy bone graft bed device for the posterior of a vertebral body according to claim 1, wherein the preparation method comprises the following steps:
step one, constructing a three-dimensional bone grafting bed model through 3D modeling;
mixing zinc cerium powder through a high-energy ball milling process to obtain degradable zinc cerium alloy powder;
and step three, printing and sintering the three-dimensional bone grafting bed model according to the established three-dimensional bone grafting bed model through a laser selection sintering process to form the degradable cerium-zinc alloy bone grafting bed device.
3. The method for preparing a bone grafting bed device of degradable zinc-cerium alloy according to claim 2, wherein the preparation of the zinc-cerium alloy in the second step comprises the following steps: weighing 1-3 parts of cerium powder and 97-99 parts of zinc powder by mass, taking a stainless steel ball mill as a mill, and uniformly mixing in an argon atmosphere by a planetary ball mill at the ball milling speed of 150rpm/min for 2-3 h to obtain the degradable zinc-cerium alloy powder.
4. The preparation method of the degradable zinc-cerium alloy bone grafting bed device according to claim 3, wherein 30min of continuous ball milling is set to be stopped for 15min, then the high-energy ball mill is reversed for 30min, and after the ball milling is completed and the tank body of the ball milling tank is completely cooled, zinc-cerium alloy powder is taken out in a vacuum glove box.
5. The method for preparing a bone grafting bed device of degradable zinc-cerium alloy according to claim 3, wherein the ball-to-material ratio between the stainless steel grinding ball and the zinc-cerium premixed powder is 10:1.
6. the method for preparing a bone grafting bed device of degradable zinc-cerium alloy according to claim 3, wherein the particle size of the zinc powder is 17-45 μm, and the purity is 99.9%; the particle size of the cerium powder is 1-5 mu m, and the purity is 99.9%; the purity of the argon gas is 99.999%.
7. The method for preparing a degradable zinc-cerium alloy bone grafting bed device according to claim 2, wherein the laser selective sintering process comprises the following steps: laying zinc-cerium alloy powder in a laser powder bed melting forming system, and printing and sintering layer by layer according to the established three-dimensional model to form a degradable cerium/zinc alloy bone grafting bed device, wherein an alternative scanning strategy is adopted, namely the scanning direction is rotated by 90 degrees compared with the previous layer; the laser scanning power is 45-55W, the scanning speed is 270-320 mm/s, and the thickness of single-layer powder is 40-60 mu m.
8. The degradable zinc-cerium alloy bone grafting bed device according to claim 1, wherein the convex surface of the net-shaped main body and the outer surface of the fixed wings of the degradable zinc-cerium alloy bone grafting bed device are frosted surfaces, the concave surface of the net-shaped main body and the inner surface of the fixed wings are smooth surfaces, and the surface treatment step of the degradable zinc-cerium alloy bone grafting bed device is as follows:
firstly, carrying out primary surface treatment on the whole bone grafting bed device by using a sand blasting process, wherein the sand blasting adopts corundum sand with the powder particle size of 80 meshes as an abrasive, the sand blasting distance is 10cm, the sand blasting pressure is 0.6-0.8 MPa, the spraying time is 1-1.5 min, and the coverage rate is more than 100%;
step two, smoothing the concave surface of the net-shaped main body of the bone grafting bed device and the inner surface of the fixed wing by utilizing a shot blasting process, wherein the shot blasting adopts glass shots with the powder particle size of 180-220 meshes as abrasive materials, the sand blasting distance is 10-15 cm, the sand blasting pressure is 0.5-0.8 MPa, the spraying time is 2-3 min, and the coverage rate is more than 100%;
thirdly, performing frosting treatment on the convex surface of the net-shaped main body of the bone grafting bed device and the outer surface of the fixed wing by using a sand blasting process, wherein the sand blasting process adopts corundum sand with the powder particle size of 24-80 meshes and glass pill mixed abrasive with the powder particle size of 180-220 meshes, and the proportion of the corundum sand to the glass pill is 4:1, the sand blasting distance is 10-15 cm, the sand blasting pressure is 3.0MPa, the spraying time is 0.5-1 min, and the coverage rate is more than 100%;
step four, cleaning the bone grafting bed device obtained in the step three: and (3) cleaning for 2-3 times by using acetone and 3-4 times by using absolute ethyl alcohol with the aid of an ultrasonic cleaning machine, wherein the cleaning time is about 10min each time, and drying by using nitrogen after cleaning.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210933903.XA CN115475278B (en) | 2022-08-04 | 2022-08-04 | Degradable zinc-cerium alloy bone grafting bed device for back of vertebral body |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210933903.XA CN115475278B (en) | 2022-08-04 | 2022-08-04 | Degradable zinc-cerium alloy bone grafting bed device for back of vertebral body |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN115475278A true CN115475278A (en) | 2022-12-16 |
| CN115475278B CN115475278B (en) | 2023-11-10 |
Family
ID=84421714
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202210933903.XA Active CN115475278B (en) | 2022-08-04 | 2022-08-04 | Degradable zinc-cerium alloy bone grafting bed device for back of vertebral body |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN115475278B (en) |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2015096271A1 (en) * | 2013-12-26 | 2015-07-02 | 西安爱德万思医疗科技有限公司 | High strength and toughness corrosion-resistant zinc alloy inplant material capable of being absorbed by human body |
| CN109350208A (en) * | 2018-11-06 | 2019-02-19 | 中南大学湘雅二医院 | A kind of titanium alloy bone grafting bed apparatus for centrum rear |
| CN110507454A (en) * | 2019-09-30 | 2019-11-29 | 山东瑞安泰医疗技术有限公司 | A kind of degradable threaded fusion cage agreeing with corpus vertebrae structure |
| CN111334688A (en) * | 2020-02-17 | 2020-06-26 | 北京大学 | Zn-RE series zinc alloy and preparation method and application thereof |
-
2022
- 2022-08-04 CN CN202210933903.XA patent/CN115475278B/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2015096271A1 (en) * | 2013-12-26 | 2015-07-02 | 西安爱德万思医疗科技有限公司 | High strength and toughness corrosion-resistant zinc alloy inplant material capable of being absorbed by human body |
| CN109350208A (en) * | 2018-11-06 | 2019-02-19 | 中南大学湘雅二医院 | A kind of titanium alloy bone grafting bed apparatus for centrum rear |
| CN110507454A (en) * | 2019-09-30 | 2019-11-29 | 山东瑞安泰医疗技术有限公司 | A kind of degradable threaded fusion cage agreeing with corpus vertebrae structure |
| CN111334688A (en) * | 2020-02-17 | 2020-06-26 | 北京大学 | Zn-RE series zinc alloy and preparation method and application thereof |
Non-Patent Citations (1)
| Title |
|---|
| YOUWEN YANG，ET AL.: "Rare earth improves strength and creep resistance of additively manufactured Zn implants", COMPOSITES PART B: ENGINEERING, vol. 216, pages 173 - 175 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN115475278B (en) | 2023-11-10 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| Murr | Open-cellular metal implant design and fabrication for biomechanical compatibility with bone using electron beam melting | |
| EP2671598A2 (en) | Implant for in-vivo insertion which is formed with a porous coating layer thereon | |
| EP2956181B1 (en) | Biodegradable metallic medical implants, method for preparing and use thereof | |
| EP0591976B1 (en) | Porous living body repairing member, and a method of imparting elasticity to it | |
| CN105247092B (en) | For the improved metal alloy of medicine equipment | |
| EP2116210A1 (en) | New knee implant and use thereof | |
| WO2016061148A1 (en) | Additive manufactured titanium bone device | |
| Revell | Tissue reactions to joint prostheses and the products of wear and corrosion | |
| Quinn | Alloplastic reconstruction of the temporomandibular joint | |
| Pham et al. | Material science in cervical total disc replacement | |
| CN102085387A (en) | In vivo absorbable metal intervertebral fusion cage | |
| Jin et al. | Mid‐and long‐term follow‐up efficacy analysis of 3D‐printed interbody fusion cages for anterior cervical discectomy and fusion | |
| Yang et al. | Application of individualized 3D-printed artificial vertebral body for cervicothoracic reconstruction in a six-level recurrent chordoma | |
| US20060020266A1 (en) | Bioabsorbable implant | |
| CN115475278B (en) | Degradable zinc-cerium alloy bone grafting bed device for back of vertebral body | |
| Hench | Prosthetic implant materials | |
| KENNEDY et al. | Radiation therapy to prevent heterotopic ossification after cementless total hip arthroplasty | |
| CN115261691B (en) | Preparation method of iron-magnesium alloy degradable bone grafting bed device | |
| Cohen et al. | Biology of implants used in head and neck surgery | |
| Dickson | Arthritis of the carpometacarpal joint of the thumb treatment by silicone sponge interposition arthroplasty: An experimental and clinical study | |
| KR20170035895A (en) | Biocompatible material in granules made of metal material or metal alloys and use of said granules for vertebroplasty | |
| Anwar et al. | Delayed catastrophic failure of a ceramic head in hybrid total hip arthroplasty | |
| Szabo et al. | Application of compact aluminum oxide ceramic implants in maxillofacial surgery | |
| CN111803244A (en) | Bone filling block with tantalum metal porous structure layer, manufacturing method and application | |
| Valcarenghi et al. | Adverse local tissue reaction after ceramic-on-ceramic total hip arthroplasty |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |