A method of improving the fatigue life of a superelastic medical device includes applying a compressive stress to a fatigue critical location of a medical device comprising a superelastic nickel-titanium alloy, where the compressive stress induces a compressive strain of greater than 9% in the fatigue critical location. After inducing the compressive strain, the compressive stress is released. A tensile stress is applied to the fatigue critical location of the medical device, where the tensile stress induces a tensile strain of greater than 9% in the fatigue critical location. After inducing the tensile strain, the tensile stress is released. After application and release of each of the compressive stress and the tensile stress, the fatigue critical location includes a non-zero amount of residual strain, and the medical device may exhibit improved fatigue properties.

A method for fabricating a bi-layer thin film is provided. A first alloy is deposited onto a substrate using a first alloy target to form a first layer of the bi-layer thin film. The first layer may comprise greater than 50 atomic % titanium (Ti) and/or less than 50 atomic % nickel (Ni). The first alloy may be deposited onto the substrate at a first temperature (e.g., room temperature). The substrate may be made of a polymer material, such as poly (4,4′-oxydiphenylene-pyromellitimide) (e.g., Kapton™). A second alloy is deposited onto the first layer using a second alloy target to form a second layer of the bi-layer thin film. The second layer may comprise greater 50 atomic % nickel and/or less than 50 atomic % titanium. The second alloy may be deposited onto the first layer at a second temperature (e.g., room temperature). The bi-layer thin film may exhibit pseudo elasticity and shape memory effect (SME).

A system, method, and apparatus for an athlete to variably control the flexibility and stiffness parameters of a piece of athletic equipment to select a desired performance characteristic of the equipment based on the stiffness parameter. According to certain embodiments discussed herein, an item of sporting equipment may be embedded, impregnated, lined, or encased using nitinol components, wherein the nitinol components may themselves be treated using a specific method in order to achieve the desired transformation results, as described below.

Disclosed herein is a composite comprising a metal alloy matrix; where the metal alloy matrix comprises aluminum in an amount greater than 50 atomic percent; a first metal and a second metal; where the first metal is different from the second metal; and where the metal alloy matrix comprises a low temperature melting phase and a high temperature melting phase; where the low temperature melting phase melts at a temperature that is lower than the high temperature melting phase; and a contracting constituent; where the contracting constituent exerts a compressive force on the metal alloy matrix at a temperature between a melting point of the low temperature melting phase and a melting point of the high temperature melting phase or below the melting points of the high and low temperature melting phases.

Shapeable guide wire devices and methods for their manufacture. Guide wire devices include an elongate shaft member having a shapeable distal end section that is formed from a linear pseudoelastic nickel-titanium (Ni—Ti) alloy that has linear pseudoelastic behavior without a phase transformation or onset of stress-induced martensite. Linear pseudoelastic Ni—Ti alloy, which is distinct from non-linear pseudoelastic (i.e., superelastic) Ni—Ti alloy, is highly durable, corrosion resistant, and has high stiffness. The shapeable distal end section is shapeable by a user to facilitate guiding the guide wire through tortuous anatomy. In addition, linear pseudoelastic Ni—Ti alloy is more durable tip material than other shapeable tip materials such as stainless steel.

Methods for controlling properties of structural elements of implantable medical devices, where the structural elements contain shape memory alloys (SMAs) include promoting or inhibiting in vivo formation of R-phase crystal structure or converging or separating the R-phase from the austenite phase.

Process for programming an orthodontic component from a shape memory material starting from an initial shape of the orthodontic component into a target shape to be programmed of the orthodontic component, wherein the target shape compared to the initial shape at least sectionally has a severe bending, the process comprising the following steps: a. providing an orthodontic component (1) of a shape memory material in an initial shape, b. creating a target baking mold for the orthodontic component (1), c. inserting the orthodontic component (1) into the target baking mold, and d. baking the orthodontic component (1) in the target baking mold in order to program it into the target shape, characterized by the following steps after step a) e. creating at least one intermediate baking mold for the orthodontic component (1), in which intermediate baking mold the orthodontic component (1) has an intermediate shape between the initial shape and the target shape, f. inserting the orthodontic component (1) into the intermediate baking mold, and g. baking the orthodontic component (1) in the intermediate baking mold.

An orthodontic bracket and archform system that uses friction-free mechanics are disclosed. The archform can have a male fastener that can be retained within an orthodontic bracket. The orthodontic bracket can have varying locking mechanism, such as deflectable tabs, springs, locking pins, and others, that can cooperate with features of the male fastener to prevent sliding between the archform and the bracket.

A wire of a nickel-titanium alloy having a permanent set of less than 5% when 11% strain is applied to the wire is disclosed. The wire may be formed by applying a first heat treatment to the wire, the first heat treatment includes applying heat of a first temperature for a first period of time, applying a strain deformation to the wire to set a shape for the wire during the first heat treatment, and applying a second heat treatment to the wire. The second heat treatment includes applying heat of a second temperature different from the first temperature for a second period of time, and the second temperature is between 210° C. and 290° C. The wire may have a modulus of at least 53 GPa when 200 MPa of stress is applied to the wire, and the wire is bonded to a secondary component.

Disclosed herein is a composite comprising a metal alloy matrix; where the metal alloy matrix comprises aluminum in an amount greater than 50 atomic percent; a first metal and a second metal; where the first metal is different from the second metal; and where the metal alloy matrix comprises a low temperature melting phase and a high temperature melting phase; where the low temperature melting phase melts at a temperature that is lower than the high temperature melting phase; and a contracting constituent; where the contracting constituent exerts a compressive force on the metal alloy matrix at a temperature between a melting point of the low temperature melting phase and a melting point of the high temperature melting phase or below the melting points of the high and low temperature melting phases.