J. Mater. Sci. Technol. ›› 2019, Vol. 35 ›› Issue (4): 535-544.DOI: 10.1016/j.jmst.2018.10.008
• Orginal Article • Previous Articles Next Articles
Ming-Shi Songab, Rong-Chang Zengc1, Yun-Fei Dingd, Rachel W. Lie, Mark Eastona, Ivan Colea, Nick Birbilisb, Xiao-Bo Chenab*()
Received:
2018-05-07
Revised:
2018-09-21
Accepted:
2018-10-03
Online:
2019-04-05
Published:
2019-01-28
Contact:
Chen Xiao-Bo
Ming-Shi Song, Rong-Chang Zeng, Yun-Fei Ding, Rachel W. Li, Mark Easton, Ivan Cole, Nick Birbilis, Xiao-Bo Chen. Recent advances in biodegradation controls over Mg alloys for bone fracture management: A review[J]. J. Mater. Sci. Technol., 2019, 35(4): 535-544.
Materials and density (g/cm3) | Composition | Young’s Modulus/Compressive Yield Strength | Surface Conditions |
---|---|---|---|
316 L SS (7.9) | Fe, Cr, Ni, Mo | 190-205 GPa/170-310MPa | Corrodes slowly |
Co-Cr-(Ni)-Mo (8.9) | Co, Cr, (Ni), Mo | 200- 250 GPa/450-1000MPa | Biocompatible |
Ti/Ti-6Al-4 V (4.5) | Ti, Al, V | 110-120 GPa/700-1200 MPa | Biocompatible |
Mg-Zn-Ca-(Sr) (1.8) | Mg, Zn, Ca (Sr) | 41-45 GPa/65-100 MPa | Bio-active (corrodes rapidly) |
Natural Bone (2.0) | Ca, P, Mg, Fe etc. | 10-40 GPa/130-180 MPa | Bio-active and conductive |
Critical Issues | Toxic elements may release into biological system | Stress shielding, leading to bone resorption and implant dislocation eventually (implantation failure) | Null or low bioactivity leads to insufficient bone growth and incurs implantation failure |
Table 1 Comparison of some critical properties of existing metallic biomaterials and Mg alloys to those of natural bone.
Materials and density (g/cm3) | Composition | Young’s Modulus/Compressive Yield Strength | Surface Conditions |
---|---|---|---|
316 L SS (7.9) | Fe, Cr, Ni, Mo | 190-205 GPa/170-310MPa | Corrodes slowly |
Co-Cr-(Ni)-Mo (8.9) | Co, Cr, (Ni), Mo | 200- 250 GPa/450-1000MPa | Biocompatible |
Ti/Ti-6Al-4 V (4.5) | Ti, Al, V | 110-120 GPa/700-1200 MPa | Biocompatible |
Mg-Zn-Ca-(Sr) (1.8) | Mg, Zn, Ca (Sr) | 41-45 GPa/65-100 MPa | Bio-active (corrodes rapidly) |
Natural Bone (2.0) | Ca, P, Mg, Fe etc. | 10-40 GPa/130-180 MPa | Bio-active and conductive |
Critical Issues | Toxic elements may release into biological system | Stress shielding, leading to bone resorption and implant dislocation eventually (implantation failure) | Null or low bioactivity leads to insufficient bone growth and incurs implantation failure |
Fig. 1. a) Galvanic series of elements in Seawater at 25 °C, b) elements comprising the human body, and c) periodic table of elements indicating essential ones for the human body.
Fig. 2. (a and b) Cross-sections from stacks of immersed plates, where the corrosion surfaces of two samples were stacked surface-to-surface on top of each other and embedded in Bakelite (see inset), for glassy Mg69Zn26Ca5 (a) and glassy Mg60Zn35Ca5 (b), with white arrows pointing to the sample surfaces. After 72 h of immersion in SBF, a thick (≈ 10 μm) porous corrosion surface is observed for Mg69Zn26Ca5, whereas a thin (≈ 3 μm) dense one evolves for Mg60Zn35Ca5. The three EDX maps below a demonstrate the occurrence of Ca, P and Zn in the corrosion layers of a. c, Close-up and corresponding EDX maps of the corrosion surface shown in b. d, Model explaining the formation of corrosion layers and their dependence on surface potential and local pH, based on the calculated Pourbaix diagram of Zn in contact with SBF. Insets: Assumed pH variation on the sample surface due to Mg dissolution [22].Reprinted with permission from Springer Nature Group according to STM (International Association of Scientific, Technical & Medical Publishers) permission guidelines.
Fig. 3. a) Equilibrium predominance diagram of calcium phosphate system calculated using Hydra-Medusa for a concentration of 10 mM PO43-. Zone A: co-existence of Ca2+ and PO43- ions; Zone B: intermediate product DCPD; and Zone C: target compound HA. (b) Surface morphology of as-primary coated Mg. Precipitation of calcium phosphate coating upon surface gives a characteristic morphology. (c) Surface morphology of secondary coated (HA coated) Mg. (d) FIB-Surface morphology of secondary HA coated Mg. coating ~ 200-300 nm thick. Images revealing profile are taken at a sample tilt of 52°.Reproduced with permission from Elsevier according to STM (International Association of Scientific, Technical & Medical Publishers) permission guidelines.
Fig. 4. Schematic illustration of self-degradation mechanism of MAO/CS composite coatings on Mg-4Li-1Ca alloys in Hank′s solution [91].Reprinted with permission from Elsevier according to STM (International Association of Scientific, Technical & Medical Publishers) permission guidelines.
Fig. 5. Schematic representation of the corrosion mechanisms of MAO/PMTMS coating [87].Reprinted with permission from Elsevier according to STM (International Association of Scientific, Technical & Medical Publishers) permission guidelines.
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