Table 1.

Mg alloys used for stent manufacturing.

Mg–Alloy	Key Features	Ref.
Mg–Zn (up to 3% Zn)	Higher affinity of adsorption to the surface of Mg–Zn alloy with the increase of Zn concentration (up to 3%).	[123]
Mg–Y (1% Y)	Adsorption of peptides is slightly weakened compared to that on the clean Mg (0001) surfaces.
Mg–Nd (1% Nd)
Mg (3.5 or 6.5%)-Li (0.5, 2 or 4%)-Zn	Good mechanical properties, degradation behavior, cytocompatibility, and hemocompatibility. Enhanced mechanical properties—yield strength, ultimate strength and elongation (twice as compared to pure Zn) and corrosion resistance without losing the viability of the Human Umbilical Vein Endothelial Cells (HUVECS) and Human Aorta Vascular Smooth Muscle Cells (VSMCS).	[124]
Mg–Al alloy AZ61	Highly susceptible to stress corrosion cracking (SCC) as compared to Zn, which is highly ductile with limited susceptibility to SCC.	[125]
MgZnYNd (coated with arginine (Arg)-based poly (ester urea urethane) (Arg–PEUU))	Super corrosion retardation, high hemocompatibility, high cytocompatibility.	[126]
Mg stent (coated with phytic acid (PA)); heparin loaded PA and bivalirudin loaded PA	Effective control on corrosion rate, biofunctional effect, good hemocompatibility, inhibits platelets adhesion, promotes endothelial cells growth superior stents compared with the bare Mg stents, super-hydrophilic surface (the contact angle being very close to zero). Hydrogen evolution vs. immersion time exhibit a slightly linear release between 5 and 10 days as compared to uncoated samples where an exponential hydrogen release was noticed within this interval.	[124]