Abstract:
A conductor that resists plastic deformation is provided for an electronic signal-carrying or electric power-carrying cable, cable assembly, or device. The conducting element itself has favorable mechanical properties and therefore combines plastic deformation resistance with conductance. In one embodiment, the superelastic conductor is fabricated using a shape memory alloy such that the transformation temperature of the superelastic conductor is set outside the useful operating range of the conductor. In another embodiment, the conductor is fabricated using a shape memory alloy that is nominally in a martensitic phase under stress free conditions. In both embodiments, the conductor microstructures are able to accommodate externally applied strain, bending, deformation, or other external displacement through mechanisms which do not involve plastic deformation.
Abstract:
Ti-Nb-Hf/Zr-(Cr) alloy shape-memory wires are provided which are suitable for use in medical devices and actuators, and methods for manufacturing such wires are provided. The present shape-memory Ti-Nb-Hf/Zr-(Cr) alloy is a superelastic wire material particularly suited for in vivo applications. For example, the present Ti-Nb-Hf/Zr-(Cr) alloy wire is radiopaque, thereby enabling surgical use of a monolithic, shape-memory alloy wire while preserving the ability to monitor the in vivo location of the wire through X-ray or other radiation-based imaging systems. In addition, the present Ti-Nb-Hf/Zr-(Cr) alloy can be manufactured to exhibit shape-memory alloy material properties without the use of nickel as an alloy constituent, thereby accommodating nickel-sensitive patients. The present Ti-Nb-Hf/Zr-(Cr) alloy can also be processed to exhibit a martensite/austenite transformation temperature near body-temperature, i.e., 37 °C, so that shape-memory effects can be utilized to accomplish work in vivo .
Abstract:
Processes for producing a nickel-titanium alloy are disclosed. The processes are characterized by the production of nickel-titanium alloy articles having improved microstructure. A pre-alloyed nickel-titanium alloy is melted and atomized to form molten nickel-titanium alloy particles. The molten nickel-titanium alloy particles are cooled to form nickel-titanium alloy powder. The nickel-titanium alloy powder is consolidated to form a fully-densified nickel-titanium alloy preform that is hot worked to form a nickel-titanium alloy article. Any second phases present in the nickel-titanium alloy article have a mean size of less than 10 micrometers measured according to ASTM E1245 - 03 (2008) or an equivalent method.
Abstract:
The invention relates to shape memory alloys. In particular, the invention relates to a shape memory alloy arrangement that includes a shape memory alloy member that is configured to undergo transformation between marten site and austenite phases in response to a change in temperature of the shape memory alloy member. The arrangement also includes a heat conductive material in contact with the shape memory alloy member wherein the heat conductive material is operable for controlling the transfer of heat to or from the shape memory alloy member by conduction. The invention also relates to a shape memory alloy actuator including the shape memory alloy arrangement of the invention. The shape memory alloy arrangement is configured to be connected to a movable object and to move the object in response to a change in temperature of the shape memory alloy member.
Abstract:
A superelastic endoprosthesis can have improved fatigue resistance, and improved resistance to crack formation by being configuring to have an austenitic finish temperature from about 5 degrees Celsius to about 35 degrees Celsius, a stress- strain curve having an upper plateau stress from about 40 ksi to about 80 ksi, and a lower plateau stress from about 5 ksi to about 50 ksi. Such an endoprosthesis may be fabricated by heating at least a portion of the endoprosthetic body in a fluid, such as air, salt bath, or fluidized sand, having a temperature from about 400 degrees Celsius to about 600 degrees Celsius for at least about 30 seconds. Additionally, only portions of an endoprosthesis may selectively be subjected to the heating parameters of the present invention such that the endoprosthesis exhibits an increased radial stiffness and an increased flexibility in the longitudinal direction.
Abstract:
Iron-manganese-silicon-based shape memory alloys comprising: (a) an effective amount of Mn greater than about 18%; (b) an effective amount of Si greater than about 5%; (c) from about 1% to about 8% Cr; (d) an effective amount of N; and (e) the balance of Fe. Preferably, the alloys comprise from about 20% to about 30% Mn, from about 5,5% to about 6% of Si, from about 2% to about 5% of Cr, from about 0,1% to about 0.5% N, and from about 61% to about 70% Fe. Preferred embodiments demonstrate about 100% shape recovery with one cylce of thermo-mechanical training with a prestain of about 3%. Methods for training the alloys are provided, comprising the steps of tensile deforming samples by applying 3.0% or 3.5& prestain at room temperature, heatin each sample to approximately 600 DEG C, and then cooling them after keeping them at this temperature for 10 minutes.
Abstract:
Disclosed is a titanium alloy comprising: 76 at.% to 89 at.% titanium; 3.0 at.% to 18 at.% of niobium; 0.5 at.% to 4.8 at.% hafnium; and 0.05 at.% to 3 at.% chromium. The alloy has superelastic properties with high elastic recovery and a large Young's modulus.
Abstract:
Systems and methods disclosed herein relate to the manufacture of metallic material with a thermal expansion coefficient in a predetermined range, comprising: deforming, a metallic material comprising a first phase and a first thermal expansion coefficient. In response to the deformation, at least some of the first phase is transformed into a second phase, wherein the second phase comprises martensite, and orienting the metallic material in at least one predetermined orientation, wherein the metallic material, subsequent to deformation, comprises a second thermal expansion coefficient, wherein the second thermal expansion coefficient is within a predetermined range, and wherein the thermal expansion is in at least one predetermined direction. In some embodiments, the metallic material comprises the second phase and is thermo-mechanically deformed to orient the grains in at least one direction.
Abstract:
A wire used in the medical field for guiding purposes, as well as in other fields, such as in the field of orthodontics for teeth aligning purposes. The wire, when prepared for use in such applications, exhibits an innovative blend of advantageous properties, including enhanced kink resistance over stainless steel wires and enhanced stiffness over Nitinol wires, which enhance its use as a medical guidewire or stylet, and further, as an arch wire in orthodontia applications.
Abstract:
A stent and a method for manufacturing a stent are provided. The stent includes a first ring having a plurality of peaks and a plurality of valleys, a second ring having a plurality of peaks and a plurality of valleys, and a connector that connects one of the peaks of the first ring to one of the valleys of the second ring. The connected peak of the first ring includes a deformed portion that extends towards the connected valley of the second ring. The method includes forming a first ring having a plurality of peaks and a plurality of valleys, forming a second ring having a plurality of peaks and a plurality of valleys, deforming a portion of at least one of the peaks of the first ring, and connecting the deformed portion of the peak of the first ring to one of the valleys of the second ring.