fig1 shows , in very schematic form , the mode of operation of a melt spinner 10 for producing rapidly solidified amorphous alloys . a melt 12 is provided in a sample container 14 , which is heatable using a heater 16 . due to the application of pressure ( shown by the arrow 18 ), the melt 12 exits from a hole at the lower end of the sample container 14 and falls on a rapidly rotating , cooled cylinder 20 made of copper ( a rotation direction of the cylinder 20 is indicated by the arrow 22 ). as a result of the very rapid cooling of the material , a transition into the crystalline state may be prevented . criteria for glass formation are particularly ( i ) low eutectics , because a low stability of the crystal and / or a higher stability of the melt is to be expected there and ( ii ) a significant size difference of the participating atoms of the alloy . for the preparation of amorphous or nanocrystalline alloys of especially suitable compositions , either binary and ternary alloy systems may be taken from the relevant data collections or may be determined experimentally in a standard way by gravimetric assays of cooling melts in heatable centrifuges . thus , for example , it is known that the binary alloy mgzn has a eutectic at 71 . 9 weight - percent magnesium and 28 . 1 weight - percent zinc . mgzn alloys of this composition or a composition near the eutectic may be produced especially easily as amorphous or nanocrystalline alloys . however , it is to be emphasized that , for many medical technology applications , the amorphous alloy system which is most thermodynamically stable is not necessarily to be selected , but rather the corrosion behavior and , of course , the biocompatibility are influencing factors for the selection of the alloy . the mechanical and thermal strains arising during the production of the medical implants are typically so low that crystallizing out of the alloys may be largely avoided . fig2 a schematically shows a vascular implant in the form of a balloon - expandable stent 10 and fig2 b shows an enlarged partial detail thereof . the stent 10 is formed by a mesh - like woven wire braid having peripheral wire sections 12 in a spiral . the stent design only has subordinate significance in the present disclosure and is thus used for illustration . the stent design illustrated in fig2 a and 2 b is laid out as balloon - expandable , i . e ., the stent design may be mechanically transferred starting from a compressed first state into an expanded second state . structures of this type are well - known in the prior art . for the implementation , the material used must meet specific criteria such as modulus of elasticity , brittleness , and strength . this may be achieved by reinforcing the webs 12 of the stent 10 using embedded fibers made of a biocorrodible amorphous or nanocrystalline magnesium alloy . the webs 12 have a wall thickness in the range from 50 - 300 μm . fig3 a and 3 b show a further vascular implant in which biocorrodible amorphous alloys are used . the vascular implant is implemented as a so - called graft stent 100 and comprises a stent - like main framework 102 and a stretchable envelope 104 which receives the main framework 102 . the main framework 102 may be designed in the way described in fig2 a and 2 b , i . e ., the main framework may comprise a biocorrodible amorphous alloy . however , a more permanent material , such as medical steel , is also conceivable . the envelope 104 comprises thin fibers of a biocorrodible amorphous magnesium alloy which are woven together . the alloy compositions of main framework 102 and envelope 104 may deviate from one another . the envelope 104 is designed in such a way that the envelope 104 is stretchable upon expansion of the main framework 102 and allows temporary coverage or even sealing of the vascular wall , e . g ., after vascular rupture . fig3 b shows a half cross - section through the graft stent 100 , which is to illustrate the relative position of the main framework 102 to the envelope 104 . fig4 shows an orthopedic implant for the osteosynthesis of fragment fractures in the area of an upper arm bone . the implant 200 has a geometry tailored to the medical function and has multiple openings through which screws 202 for fixation of the implant 200 on the bone to be fixed are guided . the implant 200 is molded from a biocorrodible composite material , which is reinforced using amorphous or nanocrystalline fibers made of magnesium or a magnesium alloy , which is to be designed in such a way that the implant may absorb the mechanical strains and loses its mechanical integrity at earliest after approximately 12 months because of the advancing biocorrosion , because it must fulfill its medical function up to this time . the screws 202 are also molded from a biocorrodible composite material , which is reinforced using amorphous or nanocrystalline fibers made of magnesium or a magnesium alloy , which displays the same corrosion behavior as the implant 200 , but does not necessarily have to comprise the same alloy composition as the implant 200 , because other requirements exist for its strength . for the intended purpose of the implant 200 and the screws 202 , biocorrodible composite materials of high strength which are reinforced using amorphous or nanocrystalline fibers are preferred . all patents , patent applications and publications referred to herein are incorporated by reference in their entirety .
a medical implant comprising a composite material which is composed of reinforcement fibers made of a magnesium - containing , bio - corrosive alloy , another bio - corrosive alloy containing a main component that is selected from the group consisting of mg , ca , fe , and y , or a non - biodegradable fiber material , embedded in a matrix made of crystalline magnesium or magnesium alloys .