A swellable packer assembly that includes a mandrel, a sealing element disposed about a least a portion of the mandrel, and a degradable metal coating disposed about at least a portion of an outer surface of the sealing element. The degradable metal coating fluidly isolates the portion of an outer surface of the sealing element from an exterior of the coating and the sealing element is formed of a material responsive to exposure to a fluid in a wellbore to radially expand from the mandrel. The degradable metal coating is selectively removable from the mandrel downhole so as to expose the sealing element to the fluid in the wellbore.

The present disclosure relates to the technical field of biomedical materials, more particularly to a degradable magnesium alloy in-situ composite anastomotic staple and a preparation method thereof. The anastomotic staple, with a composite structure, is mainly composed of Mg—Zn—Nd magnesium alloy with high strength and good plasticity (internal part), and corrosion-resistant MgF.sub.2 (external part), and is formed by in-situ synthesis of MgF.sub.2 with the outer layer of Mg—Zn—Nd magnesium alloy anastomotic staple. The magnesium alloy composite anastomotic staple provided by the present disclosure has good plastic deformation ability and mechanical strength, a low degradation rate, and a high biosafety level, which can meet the in-vivo implantation requirements. In addition, it can gradually degrade in vivo after achieving the medical effects in vivo, avoiding a second operation for removal.

The present disclosure relates to the technical field of biomedical materials, more particularly to a degradable magnesium alloy in-situ composite anastomotic staple and a preparation method thereof. The anastomotic staple, with a composite structure, is mainly composed of Mg—Zn—Nd magnesium alloy with high strength and good plasticity (internal part), and corrosion-resistant MgF.sub.2 (external part), and is formed by in-situ synthesis of MgF.sub.2 with the outer layer of Mg—Zn—Nd magnesium alloy anastomotic staple. The magnesium alloy composite anastomotic staple provided by the present disclosure has good plastic deformation ability and mechanical strength, a low degradation rate, and a high biosafety level, which can meet the in-vivo implantation requirements. In addition, it can gradually degrade in vivo after achieving the medical effects in vivo, avoiding a second operation for removal.

Provided is a multilayer zinc alloy plated steel material comprising a base steel material and multiple plating layers formed on the base steel material, wherein each of the multiple plating layers includes one of a Zn plating layer, a Mg plating layer, and a Zn—Mg alloy plating layer, and the ratio of the weight of Mg contained in the multiple plating layers to the total weight of the multiple plating layers is from 0.13 to 0.24.

Provided is a multilayer zinc alloy plated steel material comprising a base steel material and multiple plating layers formed on the base steel material, wherein each of the multiple plating layers includes one of a Zn plating layer, a Mg plating layer, and a Zn—Mg alloy plating layer, and the ratio of the weight of Mg contained in the multiple plating layers to the total weight of the multiple plating layers is from 0.13 to 0.24.

A corrodible downhole article includes a magnesium alloy, including: a strengthening metallic element comprising at least one of Al, Zn, Mn, Cu and Ag and at least one corrosion promoting element in an amount of 0.01-10 wt % in total. The alloy has a corrosion rate of at least at least 75 mg/cm.sup.2/day in 15% KC1 at 93° C. and a 0.2% proof strength of at least 100MPa when tested using standard tensile test method ASTM B557-10. In particular, the magnesium alloy includes 5-10 wt % Al, and at least one of Zn and Mn in a total amount ranging from 0 to 1.0 wt %.

A corrodible downhole article includes a magnesium alloy, including: a strengthening metallic element comprising at least one of Al, Zn, Mn, Cu and Ag and at least one corrosion promoting element in an amount of 0.01-10 wt % in total. The alloy has a corrosion rate of at least at least 75 mg/cm.sup.2/day in 15% KC1 at 93° C. and a 0.2% proof strength of at least 100MPa when tested using standard tensile test method ASTM B557-10. In particular, the magnesium alloy includes 5-10 wt % Al, and at least one of Zn and Mn in a total amount ranging from 0 to 1.0 wt %.

Provided is an implant magnesium alloy having corrosion resistance, mechanical strength, ductility at the same time. In one aspect of the present invention, an implant magnesium alloy contains: x at % of Zn; a total of y at % of at least one element of Ca and Sr; and the balance of Mg and inevitable impurities. x and y satisfy formulae 1 and 2:

0.15≤x≤1.5  (Formula 1)

0.5≤y≤1.5.  (Formula 2)

A magnesium alloy containing, in % by mass, 0.95 to 2.00% of Zn, 0.05% or more and less than 0.30% of Zr, 0.05 to 0.20% of Mn, and the balance consisting of Mg and unavoidable impurities, wherein the magnesium alloy has a particle size distribution with an average crystal particle size from 1.0 to 3.0 μm and a standard deviation of 0.7 or smaller.

A magnesium alloy containing, in % by mass, 0.95 to 2.00% of Zn, 0.05% or more and less than 0.30% of Zr, 0.05 to 0.20% of Mn, and the balance consisting of Mg and unavoidable impurities, wherein the magnesium alloy has a particle size distribution with an average crystal particle size from 1.0 to 3.0 μm and a standard deviation of 0.7 or smaller.