JPH0678989A - Biomaterial - Google Patents

Abstract

PURPOSE:To provide an excellent biomaterial having a new mode and rich in safety and reliability. CONSTITUTION:A biomaterial 11 is formed of a shape memory material obtained by quenching and coagulating an alloy molten metal showing shape memory phenomenon, and this shape memory material is formed of a Ti-Ni-Cu shape memory alloy, for example, obtained by quenching and coagulating a Ti-Ni-Cu alloy molten metal.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a biomaterial used for treating an affected part of a living body, and more particularly to a biomaterial using a shape memory material.

[0002]

2. Description of the Related Art Conventionally, various biomaterials have been used in the medical field for the purpose of treating an affected part of a living body. For example, when treating a trochanteric fracture of the femur,
For the purpose of reinforcing and connecting a fractured part, insertion of a bone marrow pin made of stainless steel preliminarily bent into an arc into the bone marrow is performed. Others, thrombus filter, expansion and contraction drive element of artificial heart, clip used for treatment of cerebral aneurysm, micropump for portable artificial kidney, hemispherical cap to cover femoral head, thrust joint used for spine , Biomaterials are used for contraceptive oviduct clips. In addition, a U-shaped staple, which plays a role like a glazing, is used when treating a bone bond or a fracture after excising a bone in a diseased part.

However, in the case of inserting the intramedullary pin made of stainless steel which is bent into a bow shape in advance into the bone marrow as described above, the tension of the intramedullary pin must be made larger than the medullary cavity in order to securely support the bone. It is not easy to insert into the bone marrow and may injure the bone in some cases. Further, in the past, when treating bones with bones or treating fractures with staples, U-shaped staples are simply driven into the bones and fixed so that the bones do not separate, so the staples tend to loosen due to body movements, There was a problem that the fixing force weakened during use.

By the way, as is well known, a shape memory alloy has a property of returning to its original shape when heated even when deformed at a certain temperature. As alloys exhibiting such a shape memory phenomenon, for example, as shown in Tables 1 and 2, Ti-Ni, Cu-Zn, Ni-Al, Fe-Mn
System alloys and the like are known.

[0005]

[Table 1]

[0006]

[Table 2]

[0007] By using the characteristics of the shape memory alloy as a biomaterial, the conventional problems in the case of using the above-mentioned general material can be solved. Treatment of an affected area is performed using the biomaterial.

[0008]

Conventionally, in the processing of shape memory alloys for forming biomaterials, it is common to finish the product material in the final shape by hot working from an alloy ingot obtained by melt casting. The melting method includes a high frequency vacuum melting method, a plasma melting method and the like, and the hot working method includes pressing, pressing and forging. Therefore, there are the following problems from the performance as a shape memory material.

(1) In the case of a Ti-Ni type alloy, which has a difficult workability peculiar to the alloy and it is difficult to obtain a thin plate product having good thermal response, Cu may be mixed especially with Cu = 10.
When it is at% or more, it becomes brittle and extremely difficult to work, and it is impossible to obtain a thin plate final product. Also,

(2) Since the polycrystalline orientation of the melt-processed material is random, the transformation time over the entire material is deviated depending on the location, and as a result, transformation strain-temperature hysteresis curve temperature range (ΔT = Af). -Mf) is large,
In addition, the bending near the loop transformation point becomes round, the response of the shape memory alloy with temperature change becomes dull, and further,

(3) The discontinuity of the transformed crystal structure causes unnecessary loss in the transformation process, and the amount of transformation strain at that time is small, which has prevented its widespread use as a biomaterial. Moreover,

(4) Since the crystal structure is coarse and the matrix dislocation density is small, the yield stress is low, and the memory effect deteriorates during repeated use (memory blur). The application range as a material was narrowed. Also,

(5) In terms of corrosion resistance, originally TiNi
Although the system is good, problems remain for long-term use in the extreme acidic / alkaline environment due to the coarse crystal grains of the processed material and the inhomogeneous surface.

Therefore, the present invention solves the above problems of the conventional biomaterials, has a sharp response with temperature change, has a good thermal-mechanical energy conversion efficiency, and has a memory effect during repeated use. Deterioration (memory blur) does not occur, and corrosion products and ion elution from bio-embedded materials that are suspected of carcinogenicity are also suppressed, and long-term in biological fluids in acidic and alkaline environments. An object is to provide a biomaterial that can be used.

It is understood that the material structure itself needs to be improved in order to minimize the defects of the shape memory alloy by the conventional melting and hot working. That is, in order to make the transformation strain-temperature hysteresis curve narrow and sharp, improve the energy conversion performance, and suppress fatigue deterioration, which is important for practical use, while increasing the strength, the alloy structure should be homogeneous, fine, and crystalline Should be arranged as much as possible so that the entire material simultaneously undergoes thermoelastic martensitic transformation. In addition, in order to improve the thermal responsiveness of the material shape and to obtain an agile shape memory phenomenon, the material shape should be made thinner to increase the specific surface area, and the heat absorption from the medium such as the outside world or the living body or the heat diffusion during cooling to the medium Need to be promoted.

In order to develop a new material satisfying the above conditions, the inventors of the present invention directly inject a molten alloy system showing a shape memory phenomenon from a nozzle to a Cu cooling roll to obtain a final thin plate (about 20 to 300 microns). Rotational rapid solidification method (M)
lt-spinning Technology) was adopted. As a result, a homogeneous and extremely fine anisotropic (columnar crystal of a few microns or less) structure can be obtained by the rapid cooling effect of the rotary rapid solidification method, and the lower structure has a high dislocation density. , It is difficult to generate plastic strain due to yield, and there is no energy loss other than phase transformation.
The inventors have found that the improvement of heat / mechanical energy conversion performance, the deterioration of shape memory fatigue, and the improvement of corrosion resistance can be achieved, and the present invention has been accomplished.

[0017]

The biomaterial according to the present invention for this purpose comprises a shape memory material obtained by rapid solidification of an alloy-based molten metal exhibiting a shape memory phenomenon.

When rapidly solidifying the alloy-based molten metal showing the shape memory phenomenon, its cooling rate is 10 ² to 10 ⁶ ° C / sec.
Is desirable. If the cooling rate is not appropriate, the quenching of the shape memory transformation of the metal structure will occur, and the shape memory effect, fatigue resistance, and corrosion resistance will deteriorate as in the case of polycrystalline.

Ti-N is used as the shape memory material.
A Ti-Ni-based shape memory alloy obtained by quenching and solidifying a molten i-based alloy is suitable, and Ti (50 ± y, y ≦ ± 2 at%)-Ni is suitable as the shape-memory material.
A Ti-Ni-Cu-based shape memory alloy obtained by rapidly solidifying a (50-y-x) -Cu (xat%)-based alloy melt is particularly suitable. As a result, a homogeneous and extremely fine anisotropic (columnar crystal of several microns or less) structure can be obtained. Furthermore, since the underlying tissue has a high dislocation density,
Since plastic strain due to yield is unlikely to occur and energy loss other than phase transformation does not occur, improvement in heat / mechanical energy conversion performance, suppression of shape memory fatigue, and improvement in corrosion resistance can be achieved.

Here, the Cu content x is 0 <x ≦ 20 at
It is good to set to%. In this region, in a normal melting / hot working process, material embrittlement (grain boundary embrittlement, etc.) occurs as the Cu content increases, and large rolling becomes difficult.

Examples of the rapid solidification method used in the present invention include, for example, a gun method in which a molten metal is directly blown onto a Cu cooling plate or the like to be rapidly cooled to produce a small test piece, a rotating roll (single or twin roll) method for producing a continuous thin plate, There are a spinning submerged spinning method suitable for producing fine wires, a spray method for producing a quenched powder, and the like.

Among the above quenching methods, when rapid solidification is performed by the rotating roll method (single roll) whose apparatus is shown in FIG. 1, the cooling rate is preferably 1 to 50 m / sec. As shown in FIG. 2, the cooling rate is 1
If it is less than m / sec, the quenched metal structure (particularly, the crystal grain size) becomes coarse and random orientation occurs, resulting in a drooping of shape memory transformation, resulting in shape memory effect, fatigue deterioration resistance, and resistance like polycrystal. Corrosion is reduced. On the contrary, when the cooling rate is higher than 50 m / sec, the metal structure becomes amorphous and the shape memory phenomenon based on the crystal transformation does not appear, which is not preferable.

[0023]

In general, when the molten metal is rapidly solidified by the molten metal quench solidification method, the metal structure is finely crystallized from the dendrite phase as the cooling speed (roll rotation speed) is increased as shown in FIG. It transforms into a crystal through a crystal at a superquenching rate (1 × 10 ⁶ ° C / sec or more). The quenching rate of the Ti-Ni-Cu molten metal is, for example, 40 m.
/ Sec (1 × 10 ⁶ ° C./sec), the metal structure becomes fine columnar crystals (crystal grain size = 2 to 3 μm) with crystal axes aligned in the plate thickness direction as shown in FIG. Even if X-ray crystal structure analysis is performed on this point, it is confirmed that the crystal directions are aligned. Therefore, Ti cooled at this quenching rate
Since the —Ni—Cu-based shape memory alloy has such a metal structure, it has the following functions.

Since the crystal orientations are aligned due to the formation of columnar crystals, the Ti-Ni-Cu-based shape memory alloy simultaneously undergoes uniform transformation as a whole. Therefore, if the crystal orientation with a large shape memory transformation strain is aligned with the longitudinal direction of the material by the rapid solidification method, the transformation strain can be increased as a whole material. Also, because of the fine columnar crystals, transformation occurs at the same time for the entire material,
As a result, the transformation temperature width ΔT becomes small and the hysteresis becomes sharp. Since it has a fine crystal structure,
The material yield stress is high and the load stress stability is improved.
Furthermore, as a result of the higher yield stress in the fine crystals and the uniform crystal orientation, plastic strain
Metastases are less likely to be introduced, and functional fatigue deterioration (memory blur) is less likely to occur.

As described above, the rapidly solidified shape memory material which is a biomaterial of the present invention has a narrow transformation temperature range and follows a smooth transformation process. No new function.
Therefore, for example, when inserting the biomaterial into the bone marrow, the biomaterial can be made into a shape that is easy to insert, and since it has extremely high corrosion resistance, it is more safe than conventional biomaterials.

Further, even when the shape memory material is used for bone bonding, it is possible to increase the bonding temperature after fixing to the living body, so that the fixing portion is prevented from loosening and reliability is improved. In that case, the yield stress is high in the biomaterial microcrystals of the present invention, and as a result that the crystal orientations are aligned, plastic strain / transition is difficult to be introduced for repeated use, and functional fatigue deterioration (memory blur) is unlikely. Become.

[0027]

EXAMPLE A wire-shaped shape-memory alloy is mainly used as a biomaterial, and this wire-shaped shape-memory alloy is manufactured by rapid solidification by, for example, the rapid solidification method in rotating liquid described above.

FIG. 9 shows an application to an intramedullary pin used for the purpose of reinforcing and connecting the fractured part in the treatment of trochanteric fracture of the femur. In FIG. 9, 11 is the above-mentioned T
It shows an intramedullary pin made of an i-Ni-Cu-based shape memory alloy, and 12 shows a femur of an animal. FIG. 9 (a)
As shown in FIG. 5, when the intramedullary pin 11 is inserted into the femur 12, the intramedullary pin has a shape that allows easy insertion into the bone marrow of the femur 12 at room temperature. After the intramedullary pin 11 has been inserted into the femur 12, the intramedullary pin 11 is moved by the body temperature of the animal.
As shown in (b), both ends bend in an arc shape more than before insertion. Therefore, the femur is securely supported by the intramedullary pin 11, and the joint limit of the femur 12 is increased.

FIG. 10 shows an example in which the biomaterial of the present invention is applied to a staple used for joining bones after excision of a diseased part and for treating a fracture.
As shown in FIG. 10 (a), the staple 21 has a U-shape that plays a role of glaze, and is used by being driven into bone.

The staple 21 is made of a Ti-Ni-Cu type shape memory alloy as an example of the biomaterial of the present invention. As shown in FIG. 10B, both ends of the staple 21 are bent and deformed inward by body temperature. That is, the staple 21 is cooled in ice water immediately before use, and is returned to its original shape by being heated by the body temperature after being attached to the bone 22. Therefore, once the staple 21 has been driven into the bone 22, the staple 21 is not loosened by the movement of the body, and the joint strength of the bone 22 can be maintained for many years.

The shape memory alloy as a biomaterial of the present invention can be applied to a stem for artificial joints. Current artificial joints are Co-Cr-Mo alloys, COP-
The mainstream is a combination of high-density polyethylene sockets and metal bones made of 1 etc., and artificial joints are fixed to bone meat using bone cement (methyl methacrylate). However, bone cement has the problems of heat of polymerization, toxicity of residual monomers, fatigue deterioration, and the like, which causes infections caused by loosening of the fixed part after surgery and stimulating reaction with foreign substances. Therefore, when the biomaterial of the present invention is applied to such an artificial joint, biotoxic substances such as carcinogens are not generated due to its extremely high yield stress and corrosion resistance, and there is no problem due to fatigue deterioration.

The biomaterial of the present invention can also be applied to an artificial heart. For example, as shown in FIG. 11, an artificial ventricle 31 that is shaped like a ventricle of the heart is created, and a large number of linear shape memory alloys 32 having a shape stored therein are attached to the surface thereof, and heating and cooling of the shape memory alloy are performed electronically. By repeating the control means using a circuit, it becomes possible to repeat the rhythmic contraction and expansion of the artificial heart.

Furthermore, the biomaterial of the present invention can be applied to a coagulation filter for treating pulmonary embolism. Pulmonary embolism is in the heart,
It occurs when blood clots in the lower limbs or pelvic veins are detached, then migrate in the blood vessels and migrate to the lungs. The biomaterial of the present invention allows the formation of a filter to trap coagulation that migrates in the vena cava. In this filter, a wire made of the biomaterial of the present invention is first subjected to a memory treatment in a shape capable of trapping coagulation, and the wire is cooled and straightened and then inserted into the vena cava using a catheter. The wire entering the vena cava functions as a coagulation filter by being heated to body temperature and immediately returning to its original complex trap shape.

The biomaterial of the present invention can also be applied as a joining wire used for treating fractures of small bones.
That is, as shown in FIG. 12, if the wire 41 made of the biomaterial of the present invention is wound around and fixed to the fractured part of the small bone 40, the superelasticity function gives a constantly stable fastening force to the fractured part, and a great therapeutic effect. Occurs.

The biomaterial of the present invention can be effectively used for the chain of ossicles. In the tympanic chamber of the eardrum, there are ossicles called incus, malleus, and stapes. The ossicles have the function of transmitting the vibration of the eardrum to the auditory nerves, but an accident or otitis media may damage or dissolve the incus bones. In such a state, the hearing ability becomes very bad. In order to deal with this problem, steel wires have been used to transmit vibrations. However, the shape and size of the thin steel wire were predetermined, and the entrance of the tympanic chamber was very narrow, making it difficult to mount and fixing it uncertain. Therefore, in order to eliminate these drawbacks, the biomaterial of the present invention can be used. That is, by forming a substitute stapes or the like in which various shapes are previously stored in the biomaterial of the present invention, an extremely good chain of ossicles can be formed.

The biomaterial of the present invention is effectively applied as an injection needle for blood transfusion and blood collection. Conventionally, a thin injection needle has been used for blood collection / transfusion from a patient with a thin blood vessel, and the blood vessel has been pierced into the blood vessel. However, due to its thin diameter, a large amount of blood collection / transfusion per unit time cannot be obtained. Therefore, by using a TiNi-based shape memory alloy pipe for this injection needle portion, the blood vessel is pierced into the blood vessel and heated to the body temperature to recover the expanded state in which the diameter is stored in advance, and blood collection / transfusion per unit time is performed. The amount can be increased and the physical and mental burden on the patient can be reduced.

The biomaterial of the present invention is effectively applied as an inter-urine dilating insert. If the urinary tract for draining urine from the kidney or the bladder is narrow due to inflammation or congenital reasons, and if urine in the body is not sufficiently discharged, stones are likely to be formed in the body. In order to prevent this and accelerate the excretion of urine to the outside of the body, a hollow shape memory alloy coil or pipe such as TiNi system is placed in the affected area, expanded in the body, and its superelasticity is also utilized. It is used as a ureteral dilator insert that conforms flexibly to the living body.

The biomaterial of the present invention is effectively applied as a fertility-preventing vas deferens and tubal stricture dilator. As a sequela of congenital and acquired inflammation, the vas deferens and fallopian tubes in the genital tract are narrowed, causing infertility because sperm and ova cannot pass through the duct. Therefore, a hollow shape memory alloy coil or pipe, such as a TiNi system, is placed in the constricted part in the affected area and expanded in the body, and its superelasticity is also used to flexibly adapt to the living body for reproductive tract expansion. Used as an insert.

The biomaterial of the present invention is effectively applied as an internal dilator for introducing an endoscope. For surgical removal of diseased parts such as the kidney, gallbladder, and liver, surgery has recently been performed under endoscopic guide through a hollow hole opened inside the body surface without making an incision. However, although a hole is made from the skin of the living body to the inside, the elasticity and resilience of the living body gradually reduce the diameter of the hole, and endoscopic surgery often becomes difficult during the operation. Therefore, in order to maintain the diameter of the hole once opened inside the living body, the diameter of the living body hole should be maintained intraoperatively by the shape memory alloy effect and the superelastic effect typified by a TiNi-based alloy in which a large inner diameter is stored in advance. You can

The biomaterial of the present invention is effectively applied as a contraceptive ring. It can also be used as a contraceptive ring of various shapes for placement inside the uterus. Since it has high biocorrosion resistance, is safe, and has a large shape memory effect, it can be easily inserted into the uterus with a linear shape and the treatment is simple.

The biomaterial of the present invention utilizes the superelasticity and high shearing force transferability of the rapidly solidified shape memory material, and uses the superelastic wire for force transfer for endoscope operation, blood vessel fixation in vivo, bone fixation. Application as a wire or board is effective.

Preferred embodiments of the biomaterial according to the present invention will be described below with reference to the drawings. In the following examples, a case where a rotating roll is used will be described as a rapid solidification method for a shape memory alloy melt. Ti-Ni having the composition shown in Table 1 obtained by arc melting a TiNiCu ingot material in an Ar atmosphere using the rotary rapid solidification apparatus shown in FIG.
The molten Cu alloy 10 is directly sprayed onto the rotating copper roll 13 from the quartz nozzle 12 around which the sample induction heating coil 11 is wound in a high-purity Ar atmosphere, and is rapidly cooled and solidified in the molten metal contact portion 14. To obtain a rapidly solidified ribbon 15.
At that time, the cooling speed was set to 1 × 10 ² to 1 × 10 ⁶ ° C./sec, the roll speed was 1 to 40 m / sec, and the rotating copper roll for cooling (diameter = 200 mm) was 100 to 4 in rotation speed.
It was set to 000 rpm. The obtained Ti-Ni-Cu-based shape memory alloy ribbon has a thickness of 0.03 to 0.6 m.
m, the width was 2.0 mm, and the length was 200 mm. The ribbon was subjected to shape memory treatment, and various characteristics shown in Table 2 were evaluated.

[0042]

[Table 1] (Alloy chemical composition)

[0043]

[Table 2] (Evaluation characteristics and evaluation conditions or evaluation methods)

The evaluation results of the above various characteristics are shown in FIGS. As shown in FIG. 3, the hysteresis curve of the quenched material is stable against increase in stress, and the hysteresis loop of the rapidly solidified Ti—Ni—Cu-based shape memory alloy is narrow and sharp as compared with the hysteresis loop of the melt-processed material. Moreover, the transformation temperature difference ΔT is kept small, and it can be said that the stability of the characteristics and functions against external load stress is high.

Further, as shown in FIGS. 4 and 5, each transformation point is the lowest at around 313 K at around 13% Cu. From this data, Ti (50 ± y, y ≦ ± 2at%)-Ni (5
In the 0-y-x) -Cu (xat%)-based alloy, the transformation point can be further adjusted to a low temperature level below room temperature by adjusting the y component or adding the fourth element (Co, Fe, etc.). For example, it is expected that the field of application as a biomaterial will spread widely.

FIGS. 6 and 7 show a Ti-Ni type shape memory alloy and a Ti-Ni-type as an example of a rapidly solidified shape memory alloy.
The fatigue deterioration resistance of the Cu-based shape memory alloy is also shown in comparison with the melt-processed material. In FIG. 6, ΔD _N represents the shape memory transformation strain width in the Nth heat cycle, and ΔD ₁ represents the shape memory transformation strain width in the _first heat cycle. N is the number of thermal cycles, Nf is the number of thermal cycles required for fracture, and N /
Nf represents a fatigue life ratio. In FIG. 7, L ₀ indicates the initial reference length, U indicates the elongation amount, and U / L ₀ indicates the elongation strain amount. As shown in FIG. 6, in the rapidly solidified Ti-Ni-Cu-based shape memory alloy, the deterioration of the transformation strain ΔD _N / ΔD ₁ changes and maintains approximately 1.0, while the melt-processed material gradually increases. Increase to. Further, as shown in FIG. 7, the rapidly solidified Ti-Ni-based shape memory alloy and the rapidly solidified Ti-Ni are used.
In the Cu-based shape memory alloy, almost no repeated elongation deterioration U / L ₀ is observed, whereas the melt-processed material also shows remarkable repeated elongation deterioration.

FIG. 8 shows the polarization curve of the Ti—Ni—Cu type shape memory alloy of this example measured in hydrochloric acid (1N / HCl). As shown in the figure, even if the lowest point of each polarization curve, that is, the so-called natural electrode potential level is compared, the corrosion resistance can be greatly improved by 100 times to 10,000 times as compared with the conventional melt processed material. To be understood.

[0048]

As described above, according to the biomaterial according to the present invention, the following effects can be obtained.

1. Since a shape memory material obtained by rapidly solidifying alloy-type molten metal exhibiting a shape memory phenomenon was applied to a biomaterial, stable and large transformation strain was exhibited even with external added stress, and it was lightweight when attached to a living body. , The feeling of discomfort is reduced, and the safety and reliability of medical care can be improved more than before.

2. Since the biomaterial is composed of a shape memory alloy obtained by quenching and solidifying an alloy-based molten metal having a shape memory phenomenon such as Ti-Ni-Cu, functional deterioration due to repeated use is significantly reduced (1/10). Degree).

3. According to the biomaterial of the present invention, the corrosion resistance in an oxidizing atmosphere (1N-HCl) hydrochloric acid is significantly improved (100 to 10,000 times). There is an excellent advantage that the generation of carcinogens in the field is prevented.

[Brief description of drawings]

FIG. 1 is a schematic diagram of a rapid solidification apparatus used to obtain a rapidly solidified shape memory alloy applied to the present invention.

FIG. 2 is a diagram showing changes in the metal structure of a shape memory alloy melt with changes in the quenching rate.

FIG. 3 is a diagram showing a shape memory transformation strain-temperature hysteresis curve of a rapidly solidified material applied to the present invention and a conventional melting / working material under each load stress.

FIG. 4 is a rapid solidification Ti—Ni— applied to the present invention.
It is a figure which shows the change of a shape memory transformation strain-temperature hysteresis curve when changing the addition amount of Cu about Cu type shape memory alloy.

FIG. 5: Rapid solidification Ti—Ni— applied to the present invention
It is a figure which shows the change of shape memory transformation temperature when changing the addition amount of Cu about Cu type shape memory alloy.

FIG. 6 is a diagram showing the degree of deterioration of the shape memory effect with repeated use (thermal fatigue) in comparison with the rapidly solidified material applied to the present invention and the melting / processing material of the comparative example.

FIG. 7 is another diagram showing the degree of deterioration of the shape memory effect due to repeated use (thermal fatigue) in comparison with the rapidly solidified material applied to the present invention and the melting / processing material of the comparative example.

FIG. 8 is a diagram showing a polarization curve of a Ti—Ni—Cu-based shape memory alloy applied to the present invention in hydrochloric acid (1N / HCl).

FIG. 9 is a diagram showing an example in which the biomaterial according to the present invention is applied to an intramedullary pin in the medical field.

FIG. 10 is a view showing an example in which the biomaterial according to the present invention is applied to a staple for treating bone fracture in the medical field.

FIG. 11 is a diagram showing an example in which the biomaterial according to the present invention is applied to an artificial heart in the medical field.

FIG. 12 is a diagram showing an example in which the biomaterial according to the present invention is applied to a chain of ossicles in the medical field.

[Explanation of symbols]

 1 Sample Induction Heating Coil 2 Quartz Nozzle 3 Rotating Cu Roll 4 Molten Metal Contact Part 5 Rapidly Solidified Ribbon 11 Intramedullary Pin as Biomaterial 21 Staple as Biomaterial

 ─────────────────────────────────────────────────── ─── Continuation of front page (72) Yasufumi Furuya, 14-1-33 Sanjo-cho, Aoba-ku, Sendai-shi, Miyagi (72) Inventor Yoshikatsu Tanahashi 10-26 (72) Kasumi-cho, Yagiyama, Taihaku-ku, Sendai-shi, Miyagi ) Inventor Ken Masumoto 3-8-22, Uesugi, Aoba-ku, Sendai City, Miyagi Prefecture

Claims (6)

[Claims] 1. A biomaterial for use in treating an affected part of a living body, which is characterized by using a shape memory material obtained by rapidly solidifying alloy-type molten metal exhibiting a shape memory phenomenon. 2. A cooling rate of 10 ² to 10 ⁶ ° C./when rapidly solidifying the alloy-based molten metal exhibiting the shape memory phenomenon
The biomaterial according to claim 1, wherein the biomaterial is sec. 3. A biomaterial used for treating an affected part of a living body, characterized by using a Ti—Ni-based shape memory alloy obtained by rapidly solidifying molten Ti—Ni alloy. . 4. A biomaterial used for treating an affected part of a living body, wherein Ti (50 ± y, y ≦ ± 2 at%)
A biomaterial, comprising a Ti-Ni-Cu-based shape memory alloy obtained by rapidly solidifying a -Ni (50-y-x) -Cu (xat%)-based alloy melt. 5. The rotating roll speed, that is, the cooling speed is set to 1 to 50 m / sec when the molten alloy system having a shape memory phenomenon is rapidly solidified by the rotating roll method.
Alternatively, the biomaterial according to claim 3 or 4. 6. The biomaterial according to claim 4, wherein the Cu content x is 0 <x ≦ 20 at%.