A method of manufacturing a medical linear member includes a step of forming a first spiral body 1 whose cross-sectional shape is a substantially substantially perfect circular shape by spirally winding a base body 3 having a plurality of arrayed wires 2 formed a shape memory alloy, around a winding core 4, a step of performing a first shape memory process on the first spiral body 1, a step of cutting the first spiral body 1 into a first predetermined length, a step of removing the winding core 4 from the cut first spiral body 1, a step of forming a second spiral body 6 whose cross-sectional shape is a flat shape by compressing the first spiral body 1 in a diametral direction, and a step of performing a second shape memory process on the second spiral body 6.

Wire products, such as round and flat wire, strands, cables, and tubing, are made from a shape memory material in which inherent defects within the material are isolated from the bulk material phase of the material within one or more stabilized material phases, such that the wire product demonstrates improved fatigue resistance. In one application, a method of mechanical conditioning in accordance with the present disclosure isolates inherent defects in nickel-titanium or NiTi materials in fields of a secondary material phase that are resistant to crack initiation and/or propagation, such as a martensite phase, while the remainder of the surrounding defect-free material remains in a primary or parent material phase, such as an austenite phase, whereby the overall superelastic nature of the material is preserved.

A circuit interconnect generally comprises an electrical connection pad, a shape memory material, and a flowable conductor. The electrical connection pad has an upper surface, a portion of which is covered by the shape memory material. The flowable conductor extends through the shape memory material and is electrically coupled to the electrical connection pad. The shape memory material has a first configuration at a first temperature and a second configuration at a second temperature. In the instance of the second temperature being greater than the first, the shape memory material has a first configuration that is substantially planar and a second configuration that is cupped.

A copper alloy disclosed in the present description has a basic alloy composition represented by Cu.sub.100(x+y)Sn.sub.xAl.sub.y (where 8x12 and 8y9 are satisfied), in which a main phase is a CuSn phase with Al dissolved therein, and the CuSn phase undergoes martensitic transformation when heat-treated or worked. A method for producing a copper alloy disclosed in the present description is a casting step of melting and casting a raw material containing Cu, Sn, and Al and having a basic alloy composition represented by Cu.sub.100(x+y)Sn.sub.xAl.sub.y (where 8x12 and 8y9 are satisfied) so as to obtain a cast material, and a homogenization step of homogenizing the cast material in a temperature range of a CuSn phase so as to obtain a homogenized material, the method includes at least the casting step.

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.

The present invention provides a method for manufacturing a medical basket treatment tool. The method for manufacturing a medical basket treatment tool having one or more wire formed using an alloy containing two or more metals includes a heating process of performing heat treatment on a target portion of at least one wire among the wires one or more times, the heat treatment irradiating the target portion with a laser with an irradiation fluence of 10.sup.3 J/cm.sup.2 or more and heating the target portion to become a predetermined temperature lower than the solid solubility limit of the alloy.

Disclosed herein is a shape memory alloy comprising 45 to 50 atomic percent nickel; and 1 to 30 atomic percent of at least one metalloid selected from the group consisting of germanium, antimony, zinc, gallium, tin, and a combination of one or more of the foregoing metalloids, with the remainder being titanium. The shape memory alloy may further contain aluminum. Disclosed herein too is a method of manufacturing the shape memory alloy.

An endodontic instrument (10) for preparing a tooth of a patient, in particular an instrument for cleaning the root canal that follows the natural geometry of the canal. The instrument (10) comprises a rigid tip (11) arranged to be mounted on a rotating support (102) of an apparatus (103), known as a contra-angle, and a working sector (12). The working sector (12) comprises a free end section (13) which is arranged to engage in the root canal (101). The working sector (12) is composed of a first essentially straight active segment (14) disposed in the extension of the rigid tip (11), and at least one second active segment (15) comprising the free end section (13). In the static state, the second active segment (15) is substantially straight and, in the dynamic state, the second active segment (15) has a curved shape.

Disclosed herein is a shape memory alloy comprising 48 to 50 atomic percent nickel, 15 to 30 atomic percent hathium, 1 to 5 atomic percent aluminum; with the remainder being titanium. Disclosed herein too is a method of manufacturing a shape memory alloy comprising mixing together to form an alloy nickel, hafnium, aluminum and titanium in amounts of 48 to 50 atomic percent nickel, 15 to 30 atomic percent hafnium, 1 to 5 atomic percent aluminum; with the remainder being titanium; solution treating the alloy at a temperature of 700 to 1300 C. for 50 to 200 hours; and aging the alloy at a temperature of 400 to 800 C. for a time period of 50 to 200 hours to form a shape memory alloy.

Exposing nitinol to a shape setting temperature while the nitinol is in an unstrained or minimally strained condition. The nitinol is then substantially deformed in shape while at elevated temperature. After deformation, the nitinol remains at the elevated temperature for a time to shape set the material. The nitinol is then returned to approximately room temperature 20? C. by means of water quenching or air cooling for example.