Additively Manufactured Biodegrabable Metal Implants
ZHENG Yufeng1(), XIA Dandan2, SHEN Yunong1, LIU Yunsong2, XU Yuqian2, WEN Peng3, TIAN Yun4, LAI Yuxiao5
1.School of Materials Science and Engineering, Peking University, Beijing 100871, China 2.Department of Prosthodontics, Peking University School and Hospital of Stomatology, National Clinical Research Center for Oral Diseases, National Engineering Laboratory for Digital and Material Technology of Stomatology, Beijing Key Laboratory of Digital Stomatology, National Medical products Administration Key Laboratory for Dental Materials, Research Center of Engineering and Technology for Digital Dentistry, Ministry of Health, Beijing 100081, China 3.State Key Laboratory of Tribology, Department of Mechanical Engineering, Tsinghua University, Beijing 100084, China 4.Department of Orthopedics, Peking University Third Hospital, Beijing 100191, China 5.Institute of Biomedical and Health Engineering, Shenzhen Institute of Advanced Technology, Chinese Academy of Sciences, Shenzhen 518055, China
Cite this article:
ZHENG Yufeng, XIA Dandan, SHEN Yunong, LIU Yunsong, XU Yuqian, WEN Peng, TIAN Yun, LAI Yuxiao. Additively Manufactured Biodegrabable Metal Implants. Acta Metall Sin, 2021, 57(11): 1499-1520.
Additive manufacturing (AM) can produce complicated structures accurately and freely, giving the implant a macro and micro geometry, which makes the implant match the patient's defect site and realize the needs for personalized clinical treatment. Thus, AM provides a new manufacturing method for biodegradable metals. Presently, biodegradable metals are the hotspot issues of metallic biomaterials research. Additively-manufactured biodegradable metals are new research field. In this paper, a comprehensive review on the AM of Mg-, Zn-, and Fe-based biodegradable metals, which focuses on their processes and influencing factors, mechanical properties, biodegradation behavior, and biocompatibility, is given. Finally, the future development trend of the AM biomedical metallic materials is explored.
Fund: National Key Research and Development Program of China(2018YFE0104200);National Natural Science Foundation of China(51931001);Open Project of NMPA Key laboratory for Dental Materials(PKUSS20200401);CAS Interdisciplinary Innovation Team(JCTD-2020-19)
About author: ZHENG Yufeng, professor, Tel: (010)62767411, E-mail: yfzheng@pku.edu.cn
Table 1 Summary of biodegradable metals' properties[12-17]
Classification
Material
Benefit
Limitation
Application
Bio-inert
316L SS
Acceptable biocompatibility, good
High elastic modulus, localized
● Joint arthroplasty
metals
corrosion resistance and MRI
corrosion with pitting, crevices and
● Bone defect repair
compatibility, low cost
stress corrosion cracking
● Dental implant
Co-Cr
High mechanical strength,
High elastic modulus, biological
● Dental (orthodontic
alloys
excellent corrosion, fatigue and
toxicity
wire)
wear resistance
● Craniofacial
● Spinal
● Orthopedic
Ti alloys
Superior biocompatibility, good
Poor tribological characteristics,
● Bone defect repair
corrosion resistance, mechanical
fatigue strength, expensive,
● Bone scaffold
strength, light weight
incompatibility between the
● Spinal fusion
elastic modulus of bone and
● Joint arthroplasty
the Ti implant material
Biodegradable
Mg-
Good biocompatibility,
Excessive degradation rate, high
● Cardiovascular stents
based
biodegradable in the physiological
H2 gas evolution, unwanted pH
● Orthopedic fixation
metals
alloys
environment, ability to stimulate
increase in surrounding tissue,
bone formation and elastic modulus
premature loss of mechanical
close to natural bone, MRI
integrity before sufficient
compatibility
tissue healing
Zn-based
Intermediate corrosion rate (faster
Age hardening, excessive release
● Cardiovascular stents
alloys
than Fe-based alloys, slower than
of Zn2+ during degradation results
● Orthopedic fixation
Mg-based alloys), fair
in cytotoxicity in vitro and delayed
compatibility, no gas evolution
osseointegration in vivo
Fe-based
High strength, high ductility, MRI
Low corrosion rate, high elastic
● Cardiovascular stents
alloys
compatibility, fair
modulus
biocompatibility, gas evolution
Table 2 Characteristics and potential applications of metallic biomaterials[20,21]
AM methodology
Characteristic
Vat polymerization
The build platform is lowered into a vat of liquid photopolymer resin. A UV light cures the
resin in layers on top of the platform.
Alternative name: SLA—stereolithography apparatus, DLP—digital light processing
Resolution: 10 μm
Material jetting
Droplets of material are deposited onto the surface using a thermal or piezoelectric method.
Each layer is cooled or cured by UV light.
Alternative name: inkjet printing, MJM—multi-jet modeling
Resolution: 25-100 μm
Material extrusion
A material spool is fed and melted through a heated nozzle and deposited onto the surface,
layer by layer.
Alternative name: FDM—fused deposition modeling
Resolution: 50-200 μm
Powder bed fusion
The material in powder form is spread over the surface and fused to other layers using a laser
or electron beam.
Alternative name: SMS—selective metal sintering, SHS—selective heat sintering, DMLS—
direct metal laser sintering
Resolution: 80-250 μm
Binder jetting
Building material in powder form is rolled/spread into a flat sheet. A liquid binding agent is
selectively applied between layers as an adhesive.
Alternative name: PB—powder bed printing
Resolution: 80-250 μm
Sheet lamination
Material in sheet form is placed on a cutting bed and bonded over the surface using an
adhesive. Each layer is cut to shape by laser, knife, or drill after bonding.
Alternative name: UC—ultrasonic consolidation, LOM—laminated object manufacturing
Resolution: depends of thickness of laminates
Direct energy deposition
Material, typically in the form of a powder or wire, is deposited onto the surface and melted
using a laser or electron beam upon deposition.
Alternative name: LMD—laser metal deposition, LENS—laser engineered net shaping
Resolution: 250 μm
Table 3 Summary of different 3D printing methodologies[22]
Fig.1 Examples of AM patient specific implants used for reconstruction of resected bone tumours and follow-up X-ray films showing placement, specifically
Fig.2 SEM images of JDBM (Mg-Nd-Zn-Zr alloy) powders fabricated by gas atomization (a)[58] and nitrogen atomized pure Zn powder (b)[59] (It is also observable that smaller particles are attached onto the surface of some powder particles (indicated by white arrows in Fig.2a), and that some powder particles have a partial shell (indicated by black arrows in Fig.2a))
Fig.3 Power-speed process map for L-PBF prepared WE43 (a)[66] and relationship between density and Ev under different powers and speeds (b)[59] (Hs—hatch spacing, Ds—layer thickness, Ev—volume energy; SLM—selective laser melting)
Fig.4 The summary of additively manufactured porous biomaterials' lattice structures
Fig.5 Timelines displaying a historical background of AM biodegradable metals research and development, biodegradable scaffolds and stents made by L-PBF (L-PBF—laser powder bed fusion) (a)[59,69,77,78,80,81,109-121], Mg-based biodegradable metals (b)[113], Zn-based biodegradable metals (c)[59], and Fe-based biodegradable metals (d)[118]
Fig.6 In vivo evaluation of AM porous Fe scaffolds
Fig.7 Tensile properties of bulk medical metallic materials manufactured by L-PBF (a)[59,112,115,116,119,123,125,127-136], elastic modulus-compressive yield strength relationship of biodegradable scaffolds manufactured by L-PBF (b)[58,78-81,118,121,142], biodegradation rates of L-PBF biodegradable metals (c)[78-80,118,119,121,128,137,144,145], and cell viability of MG63 and MC3T3-E1 cell lines in L-PBF biodegradable metals' extractions (The unmarked parts are the cell viabilities of MG63) (d)[58,78-81,118,121,128,137,151,152]
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