Preparation of Biodegradable Mg-Based Composites and Their Recent Advances in Orthopedic Applications
OUYANG Sihui1,2,3, SHE Jia1,2,3, CHEN Xianhua1,2(), PAN Fusheng1,2
1 National Engineering Research Center for Magnesium Alloys, Chongqing University, Chongqing 400044, China 2 College of Materials Science and Engineering, Chongqing University, Chongqing 400044, China 3 Lanxi Magnesium Materials Research Institute, Lanxi 321100, China
Cite this article:
OUYANG Sihui, SHE Jia, CHEN Xianhua, PAN Fusheng. Preparation of Biodegradable Mg-Based Composites and Their Recent Advances in Orthopedic Applications. Acta Metall Sin, 2025, 61(3): 455-474.
Biodegradable Mg-based materials have emerged as a promising class of orthopedic implants in the 21st century, owing to their excellent osteogenic properties and an elastic modulus similar to that of cortical bone. This review summarizes the current applications and development trends of Mgbased composites in bone repair. First, the fabrication methods of Mg-based composites, along with their advantages and disadvantages, are discussed. Second, the impact of reinforcement on the mechanical properties and degradation behavior of these composites is examined. Third, preclinical studies on the use of Mg-based composites in fracture fixation and bone defect repair are reviewed, confirming their bioactivity and clinical safety. Fourth, the effects of the degradation behavior of Mg-based composites on stem cell osteogenic differentiation and the related molecular mechanisms are explored. Finally, the challenges of applying Mg-based composites for bone repair based on existing preclinical studies are outlined, and potential future advancements are proposed.
Fund: National Funds for Distinguished Young Scholars(52225101);National Natural Science Foundation of China(52301132);Fundamental Research Funds for the Central Universities(2023CDJYXTD-002)
Corresponding Authors:
CHEN Xianhua, professor, Tel: (023)65102633, E-mail: xhchen@cqu.edu.cn
Fig.1 Schematic of the preparation process of nano-diamond (ND) reinforced ZK60 composite via powder metallurgy[25] (F—force) (a) and microstructures[25,29] (b-d) (b) SEM image of ND/ZK60 composite, corresponding grain size distribution, and TEM and high-resolution TEM (HRTEM) images at the interface[25] (Inset in Fig.1b is selected area electron diffraction (SAED) pattern in the corresponding region) (c) schematic of the preparation process of Ti/AZ61 composite prepared by spark plasma sintering (SPS)[29] (d) electron backscatter diffraction (EBSD) and SEM images and kernel average misorientation (KAM) results of Ti/AZ61 composite (LAGBs—low angle grain boundaries, HAGBs—high angle grain boundaries)[29]
Fig.2 Schematics of the ultrasonic-assisted stir casting process[33] (a) and ultrasonic-assisted semi-solid stirring method for preparing graphene-reinforced Mg-based composites[37] (b) and microstructures and mechanical properties[39,40] (c, d) (c) SEM image of nano-SiC reinforced Mg-Zn-based composites; Fourier-filtered atomic-resolution TEM image of SiC/Mg interface; compression engineering stress-strain curve and in situ SEM images of micro-pillar tests (Insets in Fig.2c are the fast Fourier transforms (FFT) of the magnesium matrix (left) and the SiC nanoparticle (right), respectively)[39] (d) comparisons of mechanical properties of Mg-based composites (Inset in Fig.2d is SEM image of extruded nano-TiC reinforced Mg-Zn-Ca composites; σUTS—ultimate tensile strength, σys—yield strength)[40]
Fig.3 Schematic of the disintegrated melt deposition process[42] (a) and SEM image and compressive stress-strain curve of ZnO/Mg-4Zn-3Gd-1Ca composites[44] (b) (Eng.—engineering)
Fig.4 Schematics of the selective laser melting process[48] (a), electron beam additive manufacturing process[49] (b), binder jetting additive manufacturing process[50] (c), and wire arc additive manufacturing process[51] (GTAW—gas tungsten arc welding) (d)
cell proliferation and osteoblastic differentiation, and reduces the
release of Mg2+
Bone joint, bone screw, and pins
[68]
phosphate
β-TCP
σUCS = 402 MPa, ε = 12.0%
Enhance bone adhesion and bone growth
Bone pin, bone screw
[69]
CPP
E = 48 GPa, σys = 320 MPa, σUTS = 337 MPa
Induce osteoblastic differentiation, do not cause inflammation, higher protein adsorption, and nontoxic to tissues
Bone tissue and joint replacements, dental implant
[60]
FA
σys = 107 MPa, σUCS = 123 MPa, ε = 5.0%
Enhance cell viability and osteoconductivity
Bone graft
[70]
Graphite
CNTs
σys = 245 MPa, σUCS = 390 MPa, ε = 15.7%
Biocompatible even in blood contact, no tissue reaction, and nontoxic to cells
Bone screw, bone plates
[71]
GNPs
σys = 230 MPa, σUTS = 407 MPa, ε = 13.0%
Hemocompatibility, cytocompatibility, and good antibacterial properties
Bone screw, bone plates
[72]
Table 1 Classifications of reinforcements in Mg-based composites and corresponding mechanical and biological properties of the composites for biomedical applications[60-72]
Fig.5 Microstructure, corrosion behavior, and mechanical properties of biomedical Mg-based composites[69,71,77] (a) SEM images, corrosion weight loss rate, and corrosion mechanism schematic of β-TCP/ZK61 composites[69] (b) surface morphologies, corrosion weight loss rate, and electrochemical polarization curves of MgO/HA/Mg compo-sites after immersion in simulated body fluid (SBF) for 168 h[77] (c) SEM images of crack propagation, dislocation slip schematic, mechanical properties, and electrochemical performance of CNTs/Mg-3Zn composites[71] (UCS—ultimate compressive strength; * represents P < 0.05)
Fig.6 Invitro cell viability tests of Mg-based composites (a) cell viability, SEM images, and fluorescence images of human fetal osteoblast progenitor (hFOB) cell lines cultured on HA/Mg-3Zn composites[81] (b) cell viabilities and OM images of mouse fibroblast (L-929) cell lines cultured on β-TCP/ZK61 composites[69] (c) cell viabilities and live/dead staining images of human osteosarcoma (MG-63) cells cultured on BG/ZK60 composites[82] (BG—bioactive glass, MBG—mesporous bioative glass)
Fig.7 In vivo animal experiments of biomedical Mg-based composites (HP represents high-purity; black arrows represent semitendinosus, white arrow represent HP Mg-based screw; BMP-2 represents bone morphogenetic protein-2, VEGF represents vascular endothelial growth factor, GAPDH represents glyceraldehyde-3-phosphate dehydrogenase, BMSCs represent bone marrow mesenchymal stem cells) (a) magnesium-based screw used for tendon-bone interface healing[85] (b) Mg-based interference screw used for tendon fixation[86] (c) Mg-based screw used for fixation of distal femur fracture[87] (d) Mg-based screw and plate system used for ulna fracture fixation[88] (e) Mg-based intramedullary nail used for fixation of femoral shaft fracture[89] (f) Mg-based ring used for anterior cruciate ligament (ACL) reconstruction[90] (g) Mg-based wire promoting meniscus regeneration[91] (h) Mg-based suture anchor and Mg-based wire used for rotator cuff tear repair[92,93]
Fig.8 Schematic of the degradation behavior of Mg-based composite implants under physiological conditions and the diffusion of released Mg2+[95,96] (a), reaction of Mg-based screws with surrounding bone tissue and cells after implantation[100] (ALP—alkaline phosphatase) (b), and release of Mg2+ from Mg-based intramedullary nails promoting periosteal stem cell (PSC) activation of calcitonin gene-related differentiation and enhancing hypoxia-inducible factor (HIF) expression in BMSCs[96,101,102] (c) (HSC—hematopoietic stem cell, CGRP—calcitonin gene related peptide, DRG—dorsal root ganglion, PDSC—periostem-derived stem cell, TRPM7—transient receptor potential melastatin 7, MagT1—magnesium transporter 1, cAMP—cyclic adenosine monophosphate, CREB—cAMP response element-binding protein, NFAT—nuclear factor of activated T-cells, PGC-1α—peroxisome proliferator-activated receptor gamma coactivator 1-Alpha, ERRα—estrogen-related receptor Alpha, BMP-2—bone morphogenetic protein 2, GAG—glycosaminoglycan, RANKL—receptor activator of nuclear factor-κB ligand)
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