JP2018057842A - Implant and method for producing implant - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an implant that is safe for a living body.SOLUTION: An angular plate as an implant includes a bone supporting plate part and a blade part. The blade part is integrally formed with the bone supporting plate part, and extends from one end of the bone supporting plate part at a predetermined angle α (0°<α<180°) relative to the bone supporting plate part. The angular plate is formed from a titanium-tantalum-based alloy containing tin. The angular plate is preferably formed from a titanium-tantalum-based alloy containing tin in which a Young's modulus is decreased by increasing a processing ratio.SELECTED DRAWING: Figure 1

Description

  The present invention relates to an implant and a manufacturing method thereof.

  Nickel-titanium alloys are shape memory alloys and can be easily deformed at temperatures below the transformation temperature range, and when the temperature is above the transformation temperature range, the shape recovers to its original shape. Focusing on the above properties of nickel titanium alloys, a number of nickel titanium alloys have been used in recent years as implant materials used in orthopedics such as fracture reinforcement. For example, it has been proposed that an intramedullary nail for reinforcing a fracture in the implant is made of a nickel titanium alloy (see, for example, Patent Document 1). In addition, it has been proposed that a spinal rod having a shape extending along a part of the spinal column in the implant is formed of a nickel titanium alloy (for example, nitinol) (see, for example, Patent Document 2). Further, it has been proposed to form an implant made of nickel titanium alloy (for example, Nitinol) for fixing a rod-like member embedded in a fractured portion of the implant with a screw (for example, see Patent Document 3).

  Further, the applicant of the present application has proposed a titanium alloy composed of tantalum (Ta), tin (Sn), and the balance of titanium (Ti) and inevitable impurities as a material compatible with a living body (for example, Patent Documents). 4).

JP 2012-196463 A International Publication WO2000 / 072770 International Publication No. WO2010 / 037038 Japanese Patent No. 5855588

  However, nickel may cause allergies in the living body. For this reason, it is preferable to form an implant with the material which does not contain nickel from a viewpoint of ensuring the safety | security of a biological body.

  Nickel titanium alloys are strong in magnetism. For this reason, when the diagnosis by MRI is performed while the implant is left in the living body, there is a possibility that the implant may generate heat due to the magnetic field generated by the MRI apparatus.

  Nickel titanium alloys have a low X-ray absorption rate. For this reason, it may take time to find the implant when the position of the implant is confirmed by an X-ray image during follow-up observation of a fracture or the like.

  In view of such circumstances, the present invention intends to provide an implant that is safely configured for a living body and a method for manufacturing the implant.

  The present invention has been made to solve the above-mentioned problems, and the implant of the present invention comprises at least a part of an alloy containing titanium, tantalum, and tin. When atomic%, it contains 15 atomic% to 27 atomic% of tantalum and 1 atomic% to 8 atomic% of tin, and the balance is composed of titanium and inevitable impurities.

  The implant of the present invention is characterized in that at least a part thereof is provided with an elastically deformable portion that can be elastically deformed.

  Moreover, the implant of this invention WHEREIN: The said elastic deformation part is comprised by the part which raised the processing rate rather than the other part, It is characterized by the above-mentioned.

  Further, the implant of the present invention is provided with a hardened portion whose hardness is higher than that of other portions, and the hardened portion is formed by heat treatment.

  In the implant of the present invention, at least a part of the alloy is subjected to aging treatment.

  In the implant of the present invention, the retention time of the alloy in the aging treatment is within 30 hours.

  In the implant of the present invention, the bone is reduced.

  In the implant of the present invention, the implant includes a portion attached to the outer peripheral surface of the bone, and the portion attached to the outer peripheral surface of the bone is formed in a plate shape.

  In the implant of the present invention, the portion attached to the outer peripheral surface of the bone is fixed to the outer peripheral surface of the bone with a screw member.

  The implant of the present invention is characterized by including a portion attached to the inside of the bone.

  The implant of the present invention is characterized by including a portion that penetrates into the broken bones.

  Moreover, in the implant of the present invention, a portion that penetrates into the broken bones is formed in a screw shape.

  In the implant of the present invention, at least a part is formed in a screw shape.

  In the implant of the present invention, at least a part is formed in a bar shape.

  Moreover, the manufacturing method of the implant of this invention is characterized by manufacturing an implant using the material comprised including the alloy containing titanium, a tantalum, and tin.

  Moreover, the manufacturing method of the implant of this invention is provided with the deformation | transformation process process which deform | transforms at least one part of the said material.

  Moreover, the manufacturing method of the implant of this invention is equipped with the aging treatment process which performs an aging treatment to at least one part of the said material, or at least one part of the intermediate body formed in the manufacture process of the said implant.

  Moreover, in the manufacturing method of the implant of the present invention, the retention time of the alloy in the aging treatment is 30 hours or less.

  The implant manufacturing method of the present invention includes a solution treatment step of performing a solution treatment on at least a part of the material or at least a part of an intermediate formed in the production process of the implant. To do.

  The method for producing an implant according to the present invention further includes a solution treatment step of performing a solution treatment on at least a part of the material or at least a part of an intermediate formed in the production process of the implant. The processing step is performed after the deformation processing step.

  In the implant manufacturing method of the present invention, in the deformation processing step, a part of the material is changed to a first processing rate, and at least a part of the material is higher than the first processing rate. The second processing rate is changed.

  Further, in the implant manufacturing method of the present invention, the material is composed of two ingots including an alloy containing titanium and tantalum, and the deformation processing step includes at least part of one ingot. A first ingot deformation processing step for performing processing to change to one processing rate, and a second ingot deformation processing for performing processing to change at least a part of another ingot to a second processing rate higher than the first processing rate. And the implant includes at least a first portion and a second portion, and the first portion is formed from an ingot that has undergone the first ingot deformation processing step, and the second portion This portion is formed from an ingot that has undergone the second ingot deformation processing step.

  Further, in the implant manufacturing method of the present invention, the implant is formed such that a portion whose processing rate is changed in the deformation processing step constitutes an elastically deformable portion that can be elastically deformed.

  According to the implant of the present invention, an excellent effect of being safe for a living body can be achieved. Moreover, according to the implant manufacturing method of the present invention, an excellent effect that an implant safe for a living body can be manufactured can be achieved.

It is a figure which shows the angled plate and screw member which are the implants in the 1st Embodiment of this invention. (A) is a perspective view of the square plate and screw member which are the implants in the 1st Embodiment of this invention, (b) is a perspective view which shows an example of the structure of the braid | blade part in a square plate, (c) is a perspective view which shows another example of the structure of the blade part in a square plate. It is a figure which shows the modification of the bone auxiliary | assistant plate part of the angled plate which is an implant in the 1st Embodiment of this invention. It is a figure which shows a mode that the square plate which is the implant in the 1st Embodiment of this invention was attached to the fracture location. It is a figure which shows the manufacturing method of the non-contact part of the square plate which is an implant in the 1st Embodiment of this invention. Ti-23Ta-3Sn alloy with a processing rate of 0%, 25%, 50%, 75% (when the whole is 100 atomic% (at%), it contains 23 atomic% tantalum and 3 atomic% or less tin) And the balance of the hardness and Young's modulus in a titanium tantalum alloy consisting of titanium and inevitable impurities (the same applies to the following). Holding time showing the relationship between the holding time and the hardness of the Ti-23Ta-3Sn alloy when aging treatment is performed on a Ti-23Ta-3Sn alloy with a processing rate of 0%, 25%, 50%, 75% -Hardness diagram. (A) is a retention time-hardness relationship diagram when performing an aging treatment at 450 ° C., (b) is a retention time-hardness relationship diagram when performing an aging treatment at 500 ° C., (c ) Is a holding time-hardness relationship diagram when performing an aging treatment at 500 ° C. after solution treatment (holding at 850 ° C. for 3 hours) on the Ti-23Ta-3Sn alloy. (A) is a figure which shows the Young's modulus according to the heat processing conditions in a Ti-23Ta-3Sn alloy with a processing rate of 0%, 25%, 50%, and 75%. (B) is a figure which shows the tensile strength according to heat processing conditions in a Ti-23Ta-3Sn alloy with a processing rate of 0%, 25%, 50%, and 75%. As a heat treatment condition, in the case of no heat treatment, when the holding time is 3 hours under the condition of 500 ° C., when the holding time is 7 hours under the condition of 500 ° C., the solution treatment is performed by holding at 850 ° C. for 3 hours. After that, the case where the holding time is 28 hours under the condition of 500 ° C. is shown. It is a figure which shows the epiphyseal plate and screw member which are the implants in the 2nd Embodiment of this invention. It is a figure which shows the modification of the epiphyseal plate which is an implant in the 2nd Embodiment of this invention. It is a figure which shows a mode that the epiphyseal plate which is the implant in the 2nd Embodiment of this invention was attached to the fracture location. It is a figure which shows the intramedullary nail which is an implant in the 3rd Embodiment of this invention. It is a figure which shows a mode that the intramedullary nail which is the implant in the 3rd Embodiment of this invention was attached to the fracture location. It is a figure which shows the nail and lag screw which are the implants in the 4th Embodiment of this invention. It is a figure which shows a mode that the nail which is the implant in the 4th Embodiment of this invention, and the lag screw were attached to the fracture location. It is a figure which shows the artificial hip joint which is the implant in the 5th Embodiment of this invention. It is a flowchart which shows the manufacturing method of the implant in embodiment of this invention. It is a flowchart which shows the manufacturing method of the implant in another embodiment of this invention. It is a flowchart which shows the manufacturing method of the implant in another embodiment of this invention.

  Embodiments of the present invention will be described below with reference to the accompanying drawings. In each drawing, there is a portion in which illustration is omitted or simplified for easy understanding. Moreover, the shape and dimensional ratio of each part in each figure are not necessarily accurate.

<1. First Embodiment>
<1-1. Overall configuration>
With reference to FIG.1 and FIG.2, the angular plate 1 which is the implant in the 1st Embodiment of this invention is demonstrated below. The angled plate 1 is an instrument for fixing a fractured portion, and includes a bone auxiliary plate portion 10 and a blade portion 11.

  The bone auxiliary plate part 10 is formed in a substantially plate shape. One plane in the thickness direction of the bone assisting plate portion 10 constitutes the inner surface 10a of the bone assisting plate portion 10. On the other hand, the other plane in the thickness direction of the bone assisting plate portion 10 constitutes the outer surface 10b of the bone assisting plate portion 10. As will be described later, the inner surface 10a of the bone assisting plate portion 10 is a surface that is brought into contact with the bone.

  As shown in FIG. 1A, the bone assisting plate portion 10 is formed so as to extend on a substantially straight line and bend toward the outer surface 10b side of the bone assisting plate portion 10 from the middle. In addition, although the bone auxiliary plate part 10 is curving gently so that it may curve in the outer surface 10b side of the bone auxiliary plate part 10 from the middle in FIG. 1 (a), it is not limited to this. For example, as shown in FIG. 2, the bone assisting plate portion 10 may be bent in an L shape toward the outer surface 10 b side of the bone assisting plate portion 10 from the middle.

  Further, the bone assisting plate part 10 has a plurality of holes 13 penetrating the bone assisting plate part 10 in the thickness direction of the bone assisting plate part 10. The plurality of holes 13 allow the plurality of screw members 12 to pass therethrough. Further, the plurality of holes 13 are arranged in a line at equal intervals along the length direction of the bone assisting plate portion 10.

  Each of the plurality of holes 13 has a shape that can be engaged with the head portion 12 a of the screw member 12. When the screw member 12 is inserted from the hole 13 toward the inner peripheral surface 10a side from the outer peripheral surface 10b side of the bone assisting plate portion 10 and the hole 13 and the head portion 12a are engaged, Movement toward the peripheral surface 10a is restricted.

  The blade part 11 is integrally formed with the bone assisting plate part 10 as shown in FIG. In addition, the blade part 11 is not limited to integral formation, The bone auxiliary plate part 10 and the blade part 11 may be connected as separate members. The blade portion 11 has one end of the bone assisting plate portion 10 (here, the end portion on the curved or bent side) so as to form a predetermined angle α (0 ° <α <180 °) with the bone assisting plate portion 10. ). Here, the side where the blade portion 11 and the bone assisting plate portion 10 face each other is defined as the inside, and the opposite side is defined as the outside.

  The blade part 11 has a belt-like plate 14 that can be inserted or penetrated into bone. Specifically, for example, as shown in FIG. 1B, the blade portion 11 has a structure in which standing portions 14 a formed so as to stand on the outer surface 11 b side of the plate 14 are provided at both ends in the width direction of the plate 14. Is given as an example. In this case, the cross section cut in parallel with the width direction of the blade part 11 is substantially U-shaped.

  The blade portion 11 is not limited to the structure described above. For example, as shown in FIG. 1C, the blade portion 11 has a plate surface 15a on the outer surface 11b side in the thickness direction of the plate 15 with respect to the plate surface 15a. A structure provided with a protruding portion 15b standing in the vertical direction may be used. The protrusion 15b extends along the length direction of the plate 15 so as to be continuous at the center in the width direction of the plate 15.

  When the rigidity of the angular plate 1 is strong, there is a risk that the angular plate 1 may damage a living body including bone when a force is applied to the fractured portion fixed by the angular plate 1. On the other hand, if the angular plate 1 can be elastically deformed, even if force is applied to the fractured portion fixed by the angular plate 1, the angular plate 1 damages a living body including bone due to the elastic deformation of the angular plate 1. You can avoid the situation. For this reason, it is preferable that the angled plate 1 includes at least a part of an elastically deformable portion that can be elastically deformed.

  As a part constituting the elastic deformable part, for example, the entire square plate 1, the bone auxiliary plate part 10, the blade part 11, the joint part of the bone auxiliary plate part 10 and the blade part 11, or the above Among these, the combination of the above part is mentioned. The elastic deformation portion may be formed of an elastically deformable material.

  Moreover, it is preferable that at least a part of the angular plate 1 is formed of a material having a reasonably low elastic limit. If it does in this way, at least one part (for example, bone auxiliary plate part 10) of the angled plate 1 can be plastically deformed easily.

<1-2. Attaching the square plate to the fractured part>
Next, referring to FIG. 3, when the bone 19 is broken into one bone portion 19 a near the end portion and the other bone portion 19 b near the main body side, the angular plate 1 is attached to the broken portion. A method of attaching will be described below. When the angular plate 1 is attached to a fractured part, as shown in FIG. 3, the bone assisting plate part 10 straddles the fractured part 18, which is the surface where the bone 19 is broken, and is one of the inner surfaces 10 a of the bone assisting plate part 10. It arrange | positions so that a part may contact | abut on the outer peripheral surface of the other bone part 19b. At this time, the vicinity of the end portion continuous with the blade portion 11 in the bone assisting plate portion 10 is curved outward, so that the outer peripheral surface of the bone portion 19b and the inner surface 10a of the bone assisting plate portion 10 do not contact each other. A non-contact portion 16 that is a portion separated from each other is formed (this non-contact portion can also be defined as a curved portion). In order to reduce the area of the non-contact portion 16, a force exceeding the elastic limit is applied to the bone assisting plate portion 10 to deform the bone assisting plate portion 10, so that the bone assisting plate portion 10 is deformed to the outer peripheral surface of the bone portion 19 b. It may be shaped to match the shape of.

  On the other hand, the blade part 11 is inserted into one bone part 19 a which is divided into two by the fracture part 18. In this state, the screw member 12 is screwed into the other bone portion 19b from the outer surface 10b side of the bone auxiliary plate portion 10 through the hole 13, and the screw member 12 is screwed into the bone portion 19b. A part of the screw members 12 may be screwed into one of the bone parts 19a. If the bone assisting plate part 10 is configured as an elastically deforming part, when the bone assisting plate part 10 is pressed toward the outer peripheral surface of the bone part 19b by the screw member 12, the bone assisting plate part 10 itself is elastically deformed to the outer peripheral surface of the bone part 19b. Can be met. Furthermore, the non-contact portion 16 is fixed at the time of fixation by deforming the blade portion 11 and the bone assisting plate portion 10 so as to exceed the elastic limit, and setting the angle α slightly smaller than the actual joining angle. Etc. elastically deform and function as an urging member, and the bone portion 19a can be pressed against the other bone portion 19b by the blade portion 11. That is, the angular plate 1 fixes the fracture portion of the bone 19 in a state where the bone portion 19 a and the bone portion 19 b which are divided by the fracture portion 18 are joined. As described above, the fracture portion of the bone 19 is joined by the angled plate 1.

<1-3. Material of square plate>
Next, a specific material of the square plate 1 will be described. The angular plate 1 is made of a titanium tantalum (Ti—Ta) -based alloy containing at least titanium (Ti) and tantalum (Ta).

  The alloy constituting the square plate 1 is not particularly limited as long as it contains at least titanium and tantalum, and may contain elements other than titanium and tantalum. For example, the alloy constituting the square plate 1 may contain tin (Sn) in addition to titanium and tantalum, and in this case, better mechanical properties can be obtained.

  Specifically, the titanium tantalum-based alloy containing tin (Sn) in the embodiment of the present invention has a tantalum of 15 atomic% or more and 27 atomic% or less and 0% when the whole is 100 atomic% (at%). It is preferable that tin is contained in an amount of not less than 8 atom% and not more than 8 atom%, with the balance being titanium and inevitable impurities. Such an alloy can not only obtain better mechanical properties, that is, high tensile strength, low Young's modulus, and moderate elastic limit, but also can obtain high biocompatibility.

  Note that the lower limit of the content of tin (Sn) may be 0 atomic% as described above. Even if Sn is not added, a titanium alloy having the mechanical properties (Young's modulus, tensile strength, and elastic deformation strain) required for the angular plate 1 can be obtained if the Ta content is 15 at% or more. It is possible.

  However, in order to further improve the mechanical properties, it is preferable to add tin (Sn) to the titanium tantalum alloy. For example, from the viewpoint of the superelastic effect of titanium tantalum-based alloys, tin (Sn) has the function of suppressing the precipitation of ω phase, which is a factor that increases the Young's modulus, and enhancing the superelastic effect of titanium tantalum-based alloys. Have. This superelasticity can flexibly cope with unintended deformation. Specifically, by applying this material to the angled plate 1, even if the bones 19 a and 19 b being treated are forcibly separated due to some impact in daily life, the separation can be flexibly performed. Thereafter, it is possible to naturally return to the original fixed state. For this reason, it is preferable to add tin (Sn) to the titanium tantalum alloy. In order to sufficiently exhibit the ω phase suppression function, the Sn content when the entire titanium alloy is 100 at% is preferably 1 at% or more.

  In addition, the titanium tantalum alloy containing tin (Sn) has a very small amount of elution of metal ions of the constituent elements Ti, Ta, and Sn, exhibits excellent corrosion resistance, has low cytotoxicity, and is biocompatible. High non-magnetic material that is hard to be magnetized by an external magnetic field and has a very low risk of adverse effects on medical devices (such as MRI) that hate magnetism, has high elasticity and appropriate rigidity, and has high workability It is an alloy. That is, the titanium tantalum-based alloy containing tin (Sn) is a titanium tantalum-based alloy having lower cytotoxicity than conventional titanium alloys and excellent in magnetic properties, corrosion resistance, mechanical properties, and workability. .

<1-3-1. Young's modulus of the material of the square plate>
Moreover, with reference to FIG. 5, the change of the Young's modulus at the time of changing the processing rate of the titanium tantalum-type alloy containing tin (Sn) is demonstrated. FIG. 5 shows the Young's modulus when the processing rate of the Ti-23Ta-3Sn alloy is 0%, 25%, 50%, and 75%. As shown in FIG. 5, when the processing rate of the Ti-23Ta-3Sn alloy is increased from 0% to 25% and when the processing rate of the Ti-23Ta-3Sn alloy is increased from 25% to 50%, both Young's modulus decreases. That is, when the processing rate of the titanium tantalum alloy containing tin (Sn) is increased, the Young's modulus of the titanium tantalum alloy is considered to decrease accordingly. On the other hand, since the surface hardness hardly changes, the fastening strength by the screw member 12 is not adversely affected.

  When attaching the angled plate 1 to the fractured part, as described above, the angled plate 1 is preferably formed so as to be elastically deformed with appropriate flexibility. For this reason, the square plate 1 is preferably formed of a titanium tantalum-based alloy containing tin (Sn) whose processing rate is increased and Young's modulus is decreased. In particular, the square plate 1 is preferably formed of a titanium tantalum-based alloy containing tin (Sn) whose processing rate is 20% or more, and more preferably, tin (Sn) whose processing rate is 40% or more. It is preferable to form by the titanium tantalum type alloy to contain.

  Note that the processing rate of only a part of the titanium tantalum-based alloy forming the square plate 1 may be changed. As a part of the angled plate 1, for example, the bone assisting plate portion 10, the blade portion 11, the joint portion between the bone assisting plate portion 10 and the blade portion 11, a combination of the above portions, or the above Some of them are listed. As a result, a portion having a low Young's modulus, flexibility and easy elastic deformation, and a portion having high rigidity can be formed on the angular plate 1.

<1-3-2. Contrastability of material of square plate>
Further, conventionally, for example, implants used in the body at the time of fracture are nickel titanium which is a stainless steel such as SUS316L or a superelastic alloy in order to obtain necessary mechanical properties (tensile strength, Young's modulus, elastic limit, etc.). These materials were composed of (Ni—Ti) based alloys and the like, but these materials had a low X-ray absorption rate and thus were difficult to be displayed in an X-ray image. In contrast, a titanium tantalum alloy has a tensile strength and Young's modulus equivalent to those of a nickel titanium alloy, which is a superelastic alloy, but has a high atomic weight because it contains tantalum having a large atomic weight (X (Line impermeability). Therefore, the angled plate 1 made of a titanium tantalum alloy has excellent contrast properties during X-ray imaging.

<1-3-3. Plastic deformation of square plate material>
Titanium tantalum alloys have a reasonably lower elastic limit than nickel titanium alloys. Therefore, since the square plate 1 is made of a titanium tantalum alloy, it can be appropriately plastically deformed by bending while obtaining the same strength and flexibility as the nickel titanium alloy. It becomes possible to easily bend and deform the bone assisting plate portion 10 so that the portion 10 follows the outer peripheral surface of the bone 19.

<1-3-4. Aging treatment of square plate material>
Next, the hardness of the titanium tantalum-based alloy when an aging treatment is performed on a titanium tantalum-based alloy containing tin (Sn) will be described with reference to FIG. This inventor performed the aging treatment at 450 degreeC and 500 degreeC with respect to the sample formed with a Ti-23Ta-3Sn alloy. The aging treatment was performed in four patterns of 1 hour, 3 hours, 7 hours, and 28 hours by putting the sample into a vacuum furnace. Four types of the above samples are prepared, and the cross-sectional diameter of each of the four types of samples is 13 (mm), and the processing rates are 0%, 25%, 50%, and 75%, respectively. And the hardness of the said 4 types of sample which performed the said aging treatment with the micro Vickers hardness tester was measured. In the micro Vickers hardness test, 13 points arranged at equal intervals (0.5 mm intervals) from the outer peripheral edge toward the center in the cross section substantially perpendicular to the axial direction of each sample were measured, and the average value of 13 points was measured. Was the test result.

  First, the case where an aging treatment is performed on the above four types of samples at 450 ° C. will be described with reference to FIG. In the sample with a processing rate of 0%, the hardness increases as the holding time becomes longer. In particular, in a sample with a processing rate of 0%, when the gradient in which the hardness increases up to 7 hours and the gradient in which the hardness increases after 7 hours are compared, the hardness after 7 hours increases. The slope is much gentler. Samples with a processing rate of 25% and 50% increase in hardness until the holding time is around 7 hours, but when the holding time is around 7 hours, the hardness decreases with a gentle gradient. In particular, in a sample with a processing rate of 25% or 50%, a comparison between a gradient in which the hardness increases up to 7 hours and a gradient in which the hardness decreases after 7 hours compares the gradient in which the hardness decreases after 7 hours. The gradient with decreasing hardness is much gentler. In addition, the gradient in which the hardness decreases after holding time of 7 hours is steeper for the sample with a processing rate of 25% than for the sample with a processing rate of 50%. A sample with a processing rate of 75% generally increases in hardness as the holding time becomes longer. In particular, in a sample with a processing rate of 75%, when the gradient in which the holding time increases to around 1 hour is compared with the gradient in which the hardness increases after 3 hours, the hardness after 3 hours increases. The slope is much gentler. Further, in the sample with a processing rate of 75%, the gradient of decreasing hardness is considerably gentle during the holding time of 1 hour to 3 hours.

  Next, the case where the aging treatment is performed on the sample at 500 ° C. will be described with reference to FIG. A sample with a processing rate of 0% increases in hardness as the holding time increases. In particular, in a sample with a processing rate of 0%, when the gradient in which the hardness increases up to 7 hours and the gradient in which the hardness increases after 7 hours are compared, the hardness after 7 hours increases. The slope is much gentler. For samples with a processing rate of 25%, the hardness increases until the holding time is up to 3 hours, and when the holding time is between 3 hours and 7 hours, the gradient of increasing hardness decreases considerably and the holding time is around 7 hours. After passing, the hardness decreases with a gentler slope. Samples with processing rates of 50% and 75% increase in hardness until the holding time is around 7 hours, but when the holding time is around 7 hours, the hardness decreases with a gentle gradient. The gradient of decreasing hardness is steeper for a sample with a processing rate of 50% than for a sample with a processing rate of 75%.

  In addition, when looking at the entire samples with processing rates of 0%, 25%, 50%, and 75%, the gradient of increasing hardness is from 1 hour to another holding time until the holding time zone is around 0 to 1 hour. Bigger than that of the band. That is, when the holding time zone exceeds about 1 hour, the gradient of increasing hardness becomes small. The holding time zone after 1 hour is the holding time zone of 1 to 3 hours, 3 to 7 hours, 7 to 28 hours, 1 to 7 hours, 1 to 28 hours, 3 to 28 hours, and other 1 hour. It refers to any subsequent time zone. Therefore, a certain degree of hardness can be obtained if the holding time in the aging treatment for the titanium tantalum alloy containing tin (Sn) is at least about 1 hour. For this reason, the retention time of the titanium tantalum-based alloy containing tin (Sn) in the aging treatment may be within 1 hour.

  Further, when the entire samples having a processing rate of 0%, 25%, 50%, and 75% are viewed together, when the holding time zone is 7 to 28 hours, the gradient in which the hardness changes is 0 to 7 hours. It is moderate compared to the case of time. That is, when the holding time zone is 7 to 28 hours, the sample has reached a certain degree of hardness, and the hardness of the sample does not change abruptly. Therefore, when the holding time zone is 7 to 28 hours, it can be considered that the hardness does not change so much even if some time passes.

  In addition, the samples with the processing rates of 25%, 50%, and 75% have a higher hardness value than the samples with the processing rate of 0% as a whole. Therefore, in order to harden the titanium tantalum-based alloy containing tin (Sn), it is preferable to subject the titanium tantalum-based alloy containing tin (Sn) to deformation processing. Examples of the deformation processing include hot processing and cold processing.

  Next, after carrying out deformation processing to make the processing rates of the above samples 0%, 25%, 50%, and 75%, respectively, the samples are held at 850 ° C. for 3 hours to perform solution treatment, Next, the case where an aging treatment is performed at 500 ° C. will be described with reference to FIG. A sample with a processing rate of 0% increases in hardness as the holding time increases. Samples with a processing rate of 25%, 50%, and 75% increase in hardness until the holding time is around 7 hours, but when the holding time is around 7 hours, the hardness decreases considerably slowly. The gradient of decreasing hardness was almost similar for all samples with processing rates of 25%, 50%, and 75%. When the solution treatment and the aging treatment are performed, it is considered that the sample has reached a certain degree of hardness and the hardness of the sample is almost constant when the holding time zone is 7 to 28 hours. I can lose weight.

  Looking at the above results in FIGS. 6 (a) to 6 (c), when the sample is subjected to aging treatment at 450 ° C. and 500 ° C., the processing time of the sample is at least the holding time. Up to about 7 hours, the hardness of the sample is increased. When the holding time exceeds about 7 hours, some hardness values increase and others decrease depending on the sample conditions. Even when the hardness value decreases, if the holding time exceeds 7 hours, the gradient at which the hardness value decreases is gentle. These are presumed to exhibit similar characteristics at other temperatures suitable for aging treatment (aging temperature). An example of the aging treatment temperature is about 300 ° C. to 600 ° C., for example. In addition, about 350 degreeC is more preferable as a minimum of aging treatment temperature. Moreover, about 550 degreeC is more preferable as an upper limit of aging treatment temperature.

  Therefore, in the aging treatment for the titanium tantalum-based alloy containing (Sn), the hardness rapidly increases until the holding time zone is about 0 to 1 hour regardless of the sample conditions, and the holding time zone is about 1 to 7 hours. In the holding time zone, the gradient in which the hardness increases further from 0 to about 1 hour becomes gentle, and in the holding time zone of 7 hours or more, the hardness decreases with a gentler gradient. For this reason, if the holding time is about 10 hours or less, it can be said that the hardness of the sample can be made near the maximum value regardless of the conditions of the sample. Therefore, the aging treatment for the titanium tantalum-based alloy containing (Sn) is preferably 10 hours or less at the aging treatment temperature, more preferably 7 hours or less. The aging treatment for the titanium tantalum-based alloy containing (Sn) may have a holding time of 1 hour or more and 7 hours or less from the viewpoint of shortening the manufacturing process time. In addition, since the hardness rapidly increases when the holding time is within 1 hour, the holding time is preferably within 1 hour when it is necessary to control the hardness within a relatively low hardness range.

  On the other hand, in the aging treatment for the titanium tantalum-based alloy containing (Sn), in the holding time zone of 7 to 28 hours, the range of change in hardness of the alloy is larger than in the case of the holding time zone of 0 to 7 hours. It can be said that the hardness of the alloy is not greatly changed. For this reason, when the holding time zone is 7 to 28 hours, there is no significant problem even if strict management in minutes or seconds is not performed in the aging process. Thereby, in the aging treatment for the titanium tantalum-based alloy containing (Sn), if the holding time zone is 7 to 28 hours, the production quality can be easily stabilized, and further the quality control cost is reduced. be able to.

  6 (a) to 6 (c), it can be estimated that the above will not change even if the holding time is extended to 30 hours. Therefore, it is not very reasonable to continue the process for 30 hours or more because of manufacturing costs. As a result, the aging treatment for the titanium tantalum-based alloy containing (Sn) has a holding time at the aging treatment temperature of 7 hours or more and 30 hours or less from the viewpoint of achieving both the manufacturing cost and the stability of the hardness of the alloy. It is preferable that it is 7 hours or more and 28 hours or less.

<1-3-5. Partial heat treatment for square plate material>
The square plate 1 formed of a titanium tantalum-based alloy containing tin (Sn) having the above-described characteristics with respect to heat treatment such as solution treatment and aging treatment is the entire material before forming the square plate 1. Alternatively, the heat treatment may be performed on part or all or part of the formed angular plate 1 to increase the hardness of the whole or part of the angular plate 1. In addition, the part which raised the hardness of the square plate 1 is called a hardening part. The cured portion in the angular plate 1 may be provided in any part of the angular plate 1. Further, there may be one or a plurality of hardened portions in the square plate 1.

  Moreover, as shown in the graph showing the relationship between the heat treatment conditions and the Young's modulus in the Ti-23Ta-3Sn alloy in FIG. 7A, Ti— which was subjected to an aging treatment with a holding time of 3 hours under the condition of 500 ° C. Comparing the Young's modulus of the 23Ta-3Sn alloy with the Young's modulus of the Ti-23Ta-3Sn alloy that has been subjected to the aging treatment for 7 hours under the condition of 500 ° C., the former Young's modulus is smaller. Moreover, the Ti-23Ta-3Sn alloy that was subjected to solution treatment by holding at 850 ° C. for 3 hours, and Ti-23Ta-3Sn alloy that was subjected to aging treatment for 28 hours under the condition of 500 ° C., Young's modulus is smaller than that of the above two conditions.

  Therefore, the Young's modulus of the Ti-23Ta-3Sn alloy can be controlled by changing the conditions of the heat treatment performed on the Ti-23Ta-3Sn alloy. This is presumed to be the same not only for the Ti-23Ta-3Sn alloy but also for the entire titanium tantalum alloy containing tin (Sn). For this reason, the Young's modulus of each part of the square plate 1 can be finely controlled by heat treatment.

  In addition, when heat-treating a part of the material before forming the angular plate 1 or a part of the angular plate 1 after forming, for example, heating the corresponding part by irradiating a laser beam is an example. Although it is mentioned, it is not limited to this, Various things including high frequency induction heating, heating by flame, heating by electron beam irradiation may be used.

  Moreover, as shown in the graph showing the relationship between the heat treatment conditions and the tensile strength in the Ti-23Ta-3Sn alloy in FIG. 7B, Ti— which was subjected to an aging treatment for 3 hours under the condition of 500 ° C. Comparing the tensile strength of the 23Ta-3Sn alloy with the tensile strength of the Ti-23Ta-3Sn alloy that had been subjected to an aging treatment for 7 hours under the condition of 500 ° C. It can be said that both have the same value and both have high tensile strength.

  Therefore, even if the aging treatment is performed on the Ti-23Ta-3Sn alloy, it is estimated that the tensile strength does not change and maintains a high tensile strength if it is at least 7 hours or less. This is presumed to be the same not only for the Ti-23Ta-3Sn alloy but also for the entire titanium tantalum alloy containing tin (Sn).

  Considering the above FIG. 6 and FIG. 7, aging for a titanium tantalum-based alloy containing tin (Sn) is required when the flexibility is required while increasing the hardness of the titanium tantalum-based alloy containing tin (Sn). The treatment is preferably about 7 hours or less. And if it is an aging treatment for 7 hours or less with respect to the titanium tantalum-type alloy containing tin (Sn), high tensile strength will be maintained.

<1-3-6. Surface modification for square plate material>
When the angular plate 1 is formed of the titanium tantalum alloy as described above, it is preferable to perform a predetermined treatment on the surface of the angular plate 1. As the predetermined process, a process for controlling the surface shape or the surface property of the square plate 1 is assumed.

  The surface shape of the angular plate 1 has a great influence on cell adhesion, progress, arrangement, aggregation, and cell differentiation / expression. In general, a rough surface has a higher cell adhesion than a smooth mirror surface. For this reason, it is preferable to perform the process which controls the surface shape with respect to the square plate 1. FIG. For example, machining (Lath-machined surface), titanium plasma spraying (Titaniumplasma-sprayed surface), blasting (Blasted surface), etching (Etched surface), SLA (Sand) Examples include -blasted large-grit acid-etched surface), spherical coated (Sintered porous-structured surface), wire electrical discharge machining, anodizing, laser light irradiation, and acid plate etching. .

  In addition, the surface properties affect not only the adsorption and adhesion of materials, proteins, bacteria, and cells important for biological reactions, but also cell proliferation and differentiation. For this reason, it is preferable to perform the process which controls the surface property with respect to the square plate 1. FIG. Examples of the treatment for controlling the surface properties of the angular plate 1 include, for example, a treatment for forming a coating layer of hydrated titania gel on the surface of the angular plate 1, and the surface of the angular plate 1 with phosphorylated amino acids and / or phosphorylated peptides. Surface treatment for coating, treatment for imparting OH groups to the coating layer on the surface of the angular plate 1, treatment for imparting a titanium phosphide layer and a calcium phosphate layer to the surface of the angular plate 1, treatment for plasma coating the surface of the angular plate 1, Examples of the treatment include coating the surface of the angular plate 1 with calcium phosphate, and performing hydrothermal alkali treatment on the surface of the angular plate 1.

<1-3-7. Angled plate material oxide film>
Further, when an oxide film is provided on the surface of the titanium tantalum alloy, the oxide film functions as a protective film and improves the corrosion resistance of the titanium tantalum alloy. Therefore, if the angled plate 1 is made of a titanium tantalum alloy provided with an oxide film, the corrosion resistance of the angled plate 1 is improved. Therefore, it is safe to leave the angled plate 1 in the body for a long period of time. In the present invention, the thickness of the oxide film provided on the surface of the titanium tantalum alloy may be controlled at the manufacturing stage.

<1-3-8. Young's modulus inclination change treatment for the material of the square plate>
Moreover, it is preferable that the angled plate 1 includes an elastic deformation portion as described above. By performing a process of changing the Young's modulus on a portion corresponding to the elastic deformation portion of the angular plate 1, the degree of elastic deformation in the elastic deformation portion can be adjusted. Various changes in the Young's modulus are assumed.

  For example, the Young's modulus gradient change mode in which the Young's modulus gradually decreases (or increases) continuously from the lower side to the upper side of the bone auxiliary plate unit 10 along the length direction of the bone auxiliary plate unit 10, Examples of the Young's modulus discontinuous change mode in which the Young's modulus changes discontinuously along the length direction of the portion 10 include, but are not limited to, examples of the Young's modulus change mode. The aspect of this may be sufficient.

  As explained above, when the titanium tantalum alloy changes the processing rate, the Young's modulus also changes. This can be realized by changing the processing rate of at least a part of the titanium tantalum alloy material by performing deformation processing on at least a part of the titanium tantalum alloy material by utilizing the characteristics of the titanium tantalum alloy. .

  The Young's modulus inclination change mode can be realized by performing deformation processing so that the processing rate is gradually increased gradually from the lower side to the upper side of the bone auxiliary plate portion 10 along the length direction of the bone auxiliary plate portion 10. It is. In addition, the Young's modulus discontinuous change mode can be realized by performing deformation processing so as to discontinuously increase the processing rate along the length direction of the bone assisting plate portion 10. That is, the elastically deformable portion can be realized by processing so as to change the processing rate in the angular plate 1 continuously or discontinuously.

  For example, as shown in the graph of the processing rate of the non-contact portion 16 shown in the right side portion of FIG. 3, the Young's modulus inclination change mode of the non-contact portion 16 changes from the top portion 16 a to the central portion 16 b of the non-contact portion 16. As it goes, it goes up in a curved line continuously, and as it goes from the center part 16b to the bottom part 16c, it goes down in a curved line continuously.

  A method of manufacturing such a non-contact portion 16 will be described below with reference to FIG. First, as shown to Fig.4 (a), the force which goes to the thickness direction of the board | plate material 700 is applied with respect to the surface of the board | plate material 700 of the titanium tantalum-type alloy containing tin (Sn). And as shown in FIG.4 (b), the surface of the board | plate material 700 is dented. As shown in FIG. 4B, the plate material 700 is recessed so as to be curved, so that the processing rate of the plate material 700 continuously changes in a curved shape. That is, the center portion of the plate material 700 has a high processing rate, and the processing rate continuously decreases toward both ends of the plate material 700.

  When a predetermined depth (up to the dotted line 701 in FIG. 4B) is cut in the thickness direction from the surface of the plate member 700 deformed as described above, the processing rate continuously changes as shown in FIG. 4C. A plate member 710 having a portion to be obtained is obtained. The angled plate 1 may be manufactured so that the portion where the processing rate of the plate material 710 continuously changes becomes the non-contact portion 16 shown in FIG.

  Further, as shown in FIG. 4 (d), as described above, the portion recessed in the curved shape shown in FIG. 4 (b) is left as it is without cutting a predetermined depth from the surface of the plate material 700 in the thickness direction. You may manufacture the square plate 1a made into the non-contact part 16. FIG.

  As shown in FIG. 5, a titanium tantalum-based alloy containing tin (Sn) has a characteristic that the Young's modulus decreases as the processing rate increases. Therefore, if the non-contact part 16 is manufactured as described above, the Young's modulus of the non-contact part 16 can be made lower than other parts. Further, as shown in FIG. 7A, a titanium tantalum-based alloy containing tin (Sn) has a characteristic that the Young's modulus increases as the holding time of the heat treatment is increased. Therefore, it is preferable that the non-contact portion 16 shortens the heat treatment holding time.

  On the other hand, the parts other than the non-contact part 16, for example, the contact part 17 and the blade part 11 that are in contact with the bone part 19 a of the bone auxiliary plate part 10, have a hardness and strength higher than those of the non-contact part 16. Higher is preferred. Therefore, it is preferable to manufacture the contact part 17 and the blade part 11 so as not to increase the processing rate. Moreover, it is preferable that the contact part 17 and the blade part 11 lengthen the heat treatment holding time.

<1-3-9. Other materials composing a square plate>
In addition, the angular plate 1 may be formed of a titanium tantalum alloy and a polymer. As the square plate 1 containing a polymer, for example, as shown in FIG. 2 (b), the peripheral portion 13a of the hole 13 of the square plate 1 is made of a polymer, and most of the other is made of a titanium tantalum alloy or the like. An example is given. As another embodiment, contrary to the above embodiment, the peripheral portion 13a of the hole 13 of the square plate 1 is formed of a titanium tantalum alloy, and the other portion is formed of a polymer or the like. Also good. An example of the polymer is polyetheretherketone (PEEK), but is not limited thereto, and other polymers may be used.

  In addition, the angular plate 1 may be formed of a titanium tantalum alloy and a biodegradable material that is biocompatible. For example, as shown in FIG. 2B, a rectangular plate 1b formed of a titanium tantalum alloy and a biodegradable material has a bone assisting plate portion near the curved portion 10e of the bone assisting plate portion 10. It is formed of two layers of a titanium tantalum alloy and a biodegradable material in a thickness direction of 10. In this case, one of the two layers 10c having a low Young's modulus (for example, the outer peripheral surface 10b side of the bone assisting plate portion 10) is formed of a titanium tantalum alloy, and the other layer 10d (for example, the bone assisting plate portion 10). The inner peripheral surface 10a side) is formed of a biodegradable material. Examples of biodegradable materials include biodegradable plastics and biodegradable metals. Biodegradable plastics are those that are hydrolyzed with acid or alkali in the living body and discharged outside the body, and examples thereof include those composed of polyglycolic acid, polydioxanone, and polylactic acid. Moreover, as a biodegradable metal, magnesium (Mg), a magnesium alloy etc. are mentioned as an example, for example.

  At the initial stage of the fracture, the repaired state of the fractured part is not sufficient, and therefore it is preferable that the rigidity of the square plate 1 attached to the fractured part is high. This is because, when the repaired state of the fracture site is not sufficient, it is preferable to give priority to firmly fixing the fracture site.

  On the other hand, after the angular plate 1 is attached to the fracture site, it is preferable that the angular plate 1 gradually becomes more easily elastically deformed as the fracture site is repaired. This is because, in order to activate osteoblasts that contribute to the repair of the fracture site, it is preferable to give priority to moving the fracture site to some extent so that excessive stress is not applied to the fracture site by the applied force.

  As described above, if the vicinity of the curved portion 10e of the bone auxiliary plate portion 10 is formed in a two-layer structure in the thickness direction of the bone auxiliary plate portion 10 using, for example, a biodegradable plastic or the like, the angular plate 1 At the initial stage of attaching the bone to the fractured portion, the degree of hydrolysis of the biodegradable plastic or the like has not progressed, so the biodegradable plastic or the like in the vicinity of the curved portion 10e of the bone assisting plate portion 10 is in a highly rigid state. As a result, the vicinity of the curved portion 10e of the bone auxiliary plate portion 10 is reinforced with biodegradable plastic or the like, and the rigidity becomes high. On the other hand, after the angled plate 1 is attached to the fractured part, the degree of hydrolysis of the biodegradable plastic or the like gradually proceeds, and the biodegradable plastic or the like gradually disappears from the body with the passage of time. For this reason, the degree of reinforcement by biodegradable plastic or the like gradually decreases, and accordingly, in the vicinity of the curved portion 10e of the bone assisting plate portion 10, the elastic deformation becomes gradually easier. The above description can be applied to biodegradable metals as appropriate according to biodegradable plastics and the like.

<2. Second Embodiment>
<2-1. Overall configuration>
The epiphyseal plate 2 that is an implant according to the second embodiment of the present invention will be described below with reference to FIGS. The epiphyseal plate 2 is mainly used for the epiphysis, and does not have the blade provided in the angular plate 1. The epiphyseal plate 2 includes a bone auxiliary plate portion 20 and an end plate portion 21.

  As shown in FIG. 8, the bone assisting plate portion 20 is formed in a plate shape like a band, and the length in the width direction of the bone assisting plate portion 20 is substantially uniform throughout. One plane in the thickness direction of the bone assisting plate portion 20 (the back surface on the paper surface) constitutes the inner surface 20a of the bone assisting plate portion 20. On the other hand, the other flat surface (the front surface of the paper surface) in the thickness direction of the bone assisting plate portion 20 constitutes the outer surface 20 b of the bone assisting plate portion 20. As will be described later, the inner surface 20a of the bone assisting plate portion 20 is a surface that is brought into contact with the bone.

  As shown in FIG. 8, the end plate portion 21 is formed in a plate shape and extends from one end (upper end) in the length direction of the bone assisting plate portion 20 to the length direction of the bone assisting plate portion 20. Further, it is integrally formed with the bone assisting plate portion 20. The end plate portion 21 has a structure that spreads outward in the width direction from the bone auxiliary plate portion 20. That is, the length of the end plate portion 21 in the width direction is longer than the length of the bone auxiliary plate portion 20 in the width direction.

  The epiphyseal plate 2 has a plurality of holes 23 and 24. The plurality of holes 23 are holes through which the screw member 22 is passed. The plurality of holes 23 are arranged in a line at equal intervals in the length direction of the bone assisting plate portion 20. Further, at least two holes 24 provided in the end plate portion 21 are arranged in a line in the width direction of the bone auxiliary plate portion 20. The screw member 22 and the holes 23 and 24 are substantially the same as the screw member 12 and the hole 13 already described with reference to FIG.

  As shown in FIG. 8, the length in the width direction of the bone assisting plate portion 20 is substantially uniform throughout the longitudinal direction, but is not limited thereto. For example, as shown in FIG. 9, the bone assisting plate portion 20 has the other end (lower end) in a direction away from the boundary (one end (upper end) of the bone assisting plate portion 20) between the bone assisting plate portion 20 and the end plate portion 21. ), The bone auxiliary plate portion 20 may be formed in a tapered shape in which the length in the width direction becomes shorter.

  Moreover, as shown in FIG. 9, the hole provided in the bone auxiliary | assistant plate part 20 and the edge part plate part 21 may have what has a diameter of various magnitude | sizes, for example. And as a screw member, as shown in FIG. 9, the thing corresponding to the magnitude | size of the diameter of a hole is used.

  Moreover, it is preferable that the epiphyseal plate 2 is provided with at least a part of an elastically deformable portion that can be elastically deformed for the same reason as described in the angular plate 1. As a part constituting the elastic deformation part, for example, the entire epiphyseal plate 2, the bone assisting plate part 20, the end part plate part 21, or the joint part of the bone assisting plate part 20 and the end part plate part 21. Or a part of the above or a combination of the above. The elastic deformation portion may be formed of an elastically deformable material.

  Moreover, it is preferable that at least a part of the epiphysis plate 2 is formed of a material having a reasonably low elastic limit. When at least a part of the epiphysis plate 2 is formed of a material having a reasonably low elasticity limit, at least a part of the epiphysis plate 2 can be easily plastically deformed.

<2-2. Attaching the epiphyseal plate to the fracture part
Next, referring to FIG. 10, when the bone 29 is broken into one bone portion 29 a near the end and the other bone portion 29 b near the main body, the epiphyseal plate 2 is attached to the broken portion. A method of attaching will be described below. When attaching the epiphyseal plate 2 to a fractured part, as shown in FIG. 10, the bone assisting plate part 20 straddles the fractured part 28, which is the fractured surface of the bone 29, and is placed on the outer peripheral surface of the bone part 29b. It arrange | positions so that the inner surface 20a of the part 20 may contact | abut. At this time, the bone assisting plate portion 20 is deformed by applying a force exceeding the elastic limit to the bone assisting plate portion 20 so that the outer peripheral surface of the bone portion 29b and the inner surface 20a of the bone assisting plate portion 20 are brought into contact with each other. Then, it may be shaped to match the shape of the outer peripheral surface of the bone part 29b.

  Further, the end plate portion 21 is brought into contact with the outer peripheral surface of one bone portion 29 a which is divided into two by the fracture portion 28. The end plate portion 21 may also be shaped so as to match the shape of the outer peripheral surface of the bone portion 29a, similarly to the bone auxiliary plate portion 20.

  In this state, the screw member 22 is screwed into the bone portion 29b through the hole 23 from the outer surface 20b side of the bone auxiliary plate portion 20, and the screw member 22 is screwed into the bone portion 29b. In addition, like the screw member 22a, you may screw together so that the bone part 29b and the bone part 29a may be straddled. Similarly, the screw member 22 is screwed into the bone portion 29a through the hole 24 from the outer surface 21b side of the end plate portion 21, and the screw member 22 is screwed into the bone portion 29a. When the screw member 22 is screwed into the bone portions 29 a and 29 b, the bone auxiliary plate portion 20 and the end plate portion 21 are elastically deformed and are in close contact with the outer peripheral surface of the bone 29. That is, the epiphyseal plate 2 fixes the fractured portion of the bone 29 in a state of straddling the fractured portion 28 and being in contact with the outer peripheral surface of the bone 29. As described above, the fracture portion of the bone 29 is joined by the epiphysis plate 2.

<2-3. Epiphyseal plate material>
The material of the epiphyseal plate 2 is <1-3. The material is the same as the material of the angled plate 1 described in <Material of the angled plate><1-3. The description of the material of the square plate> is applicable to the epiphyseal plate 2.

<3. Third Embodiment>
<3-1. Overall configuration>
An intramedullary nail 3 that is an implant according to a third embodiment of the present invention will be described below with reference to FIGS. The intramedullary nail 3 is a so-called ender nail. As shown in FIG. 11, the intramedullary nail 3 includes a linear portion 30 and a head portion 31.

  The linear portion 30 is formed in a linear shape or a rod shape. Examples of the linear portion 30 include, but are not limited to, a cross section whose shape is a curved shape such as a circle or an ellipse, or a polygon such as a rectangle or a pentagon. Instead, it may have any cross-sectional shape. Further, as shown in FIG. 11, the linear portion 30 has, for example, an arcuate shape, but can be bent or bent in another manner using a predetermined instrument. You may comprise as follows.

  The head portion 31 is a portion formed in a plate shape at one end of the linear portion 30. The head 31 has a structure that spreads outward in the width direction of the linear portion 30 from both ends of the linear portion 30 in the width direction. That is, the length in the width direction of the head portion 31 is longer than the length in the width direction of the linear portion 30.

  In addition, the intramedullary nail 3 preferably includes at least a part of an elastically deformable portion that can be elastically deformed for the same reason as described for the angular plate 1. As a part constituting the elastic deformation part, for example, the entire intramedullary nail 3, the linear part 30, the head part 31, the joint part between the linear part 30 and the head part 31, or the above Or a combination of the above parts. The elastic deformation portion may be formed of an elastically deformable material.

  Moreover, it is preferable that at least a part of the intramedullary nail 3 is formed of a material having a reasonably low elastic limit. When at least a part of the intramedullary nail 3 is formed of a material having a reasonably low elastic limit, at least a part of the intramedullary nail 3 can be easily plastically deformed. Thereby, the intramedullary nail 3 can be deformed in accordance with the shape and thickness of the patient's bone.

<3-2. Attaching the intramedullary nail to the fractured part>
Next, referring to FIG. 12, when the bone 39 fractures in one bone portion 39 a near the end and the other bone portion 39 b on the main body side, the intramedullary nail 3 is moved to the fracture portion. A method of attaching will be described below. When the intramedullary nail 3 is attached to a fractured part, for example, the bone part 39b that is divided into two parts by breaking the bone 39 across the fractured part 38 that is a fractured surface of the bone 39 and the linear part 30 inside the bone part 39a. Pass through. Then, the head portion 31 is arranged below the other bone portion 39b (distal side with respect to the one bone portion 39a).

  When three intramedullary nails 3 are inserted into the bone 39, for example, the two intramedullary nails 3 are passed in parallel, and the remaining one intramedullary nail 3 crosses the two in the middle. Insert into 39. Specifically, the two intramedullary nails 3 are inserted in the longitudinal direction from holes 39d and 39e formed in one side surface 39c of the distal end in the longitudinal direction of the bone portion 39b with respect to the bone portion 39a. In the middle of the longitudinal direction, the tip pierces the bone portion 39a so as to be folded back while abutting against one inner side surface 39f of the bone portion 39b. The remaining one intramedullary nail 3 is inserted in the longitudinal direction from the hole 39h formed in the other side surface 39g of the distal end in the longitudinal direction of the bone portion 39b with respect to the bone portion 39a. The tip is pierced into the bone portion 39a so as to be folded back while being in contact with one inner side surface 39i of the bone portion 39b. Therefore, the posture of the bone 39a is stabilized as a result of being held by the plurality of intramedullary nails 3 having different traveling directions. In this way, the three intramedullary nails 3 straddle the fracture portion 38, penetrate the inside of the bone portion 39b, and fix the bone portion 39a to the bone portion 39b.

<3-3. Intramedullary nail material>
The material of the intramedullary nail 3 is <1-3. The material is the same as the material of the angled plate 1 described in <Material of the angled plate><1-3. The explanation of the material of the angled plate> can be applied to the intramedullary nail 3.

<4. Fourth Embodiment>
<4-1. Overall configuration>
A nail 4 and a lag screw 5 which are implants in the fourth embodiment of the present invention will be described below with reference to FIGS. 13 and 14. The nail 4 is inserted into the medullary cavity from the proximal end side of the femur, for example, and is configured by a substantially columnar member. As shown in FIG. 13, for example, the nail 4 is a substantially columnar member formed in a tapered shape so that it can be easily inserted into the medullary cavity, but is not limited thereto. It may be formed in other shapes.

  The nail 4 is provided with a plurality of holes 42 penetrating the nail 4 in the radial direction (thickness direction) of the nail 4, for example. The screw member 41 is passed through the hole 42. The holes 42 are arranged in a line at equal intervals along the length direction of the nail 4. Further, a through-hole 43 that penetrates the nail 4 obliquely at a predetermined angle β (0 ° <β <90 °) with respect to the radial direction (thickness direction) of the nail 4 is provided above the nail 4 in the length direction. Provided.

  The lag screw 5 is configured by a substantially cylindrical member. A screw groove 51 is formed at the tip of a substantially cylindrical member constituting the lag screw 5. As shown in FIG. 13, the lag screw 5 is passed through the through hole 43 of the nail 4. When the lag screw 5 is passed through the through hole 43, the lag screw 5 penetrates the nail 4 obliquely with a predetermined angle β (0 ° <β <90 °) with respect to the radial direction of the nail 4.

  Moreover, it is preferable that the nail 4 and the lag screw 5 are provided with an elastic deformation part which can be elastically deformed at least in part. As a part which comprises an elastic deformation part, the nail 4 or the lag screw 5, or some of the above, or the combination of the above parts is mentioned, for example. The elastic deformation portion may be formed of an elastically deformable material.

  Moreover, it is preferable that at least a part of the nail 4 and the lag screw 5 is formed of a material having a reasonably low elastic limit. When at least a part of the nail 4 and the lag screw 5 is formed of a material having a reasonably low elastic limit, at least a part of the nail 4 and the lag screw 5 (for example, the nail 4) can be easily plastically deformed. .

<4-2. Attaching the nail and lag screw to the broken part>
Next, a method for attaching the nail 4 and the lag screw 5 to the fracture portion will be described with reference to FIG. For example, as shown in FIG. 14, the case where the nail 4 and the lag screw 5 are used when a fracture is made between the femoral body 49a and the bone head 49b of the femur 49 will be described as an example. First, the nail 4 is inserted into the medullary cavity 48 from the proximal end side of the femur 49.

  Then, the lag screw 5 is screwed into the femoral head 49b from the femur body 49a so as to cross the fractured portion 47 and penetrate the through hole 43, and the lag screw 5 is screwed into the femur 49. As a result, the lag screw 5 pulls the bone head 49b toward the femoral body 49a and joins the femur body 49a and the bone head 49b.

  In this state, the screw member 41 is screwed into the hole 42 of the nail 4 from the outer peripheral surface 49c side of the femur body 49a, and the screw member 41 is screwed into the femur 49. As a result, the nail 4 is fixed in posture within the femur 49 by the lag screw 5 above itself and is fixed in the femur 49 by the screw member 41 below itself. As described above, the fracture portion of the femur 49 is joined by the nail 4 and the lag screw 5.

<4-3. Material of nail and lag screw>
The material of the nail 4 and the lag screw 5 is <1-3. The material is the same as the material of the angled plate 1 described in <Material of the angled plate><1-3. The description of the material of the rectangular plate> can be applied to the nail 4 and the lag screw 5.

<5. Fifth embodiment>
<5-1. Overall configuration>
With reference to FIG. 15, an artificial hip joint 6 that is an implant according to a fifth embodiment of the present invention will be described below. The artificial hip joint 6 includes a stem 61, a head ball 62, a liner 63, and a socket 64. For example, the stem 61 is fixed by being inserted into the femur. In order to improve fixation with bones such as the femur, the surface of the stem 61 is coated with, for example, hydroxyapatite.

  The head ball 62 is a ball-like member having an engagement hole 62a that engages with the tapered portion 61a. When the engaging hole 62 a of the head ball 62 is inserted into the tapered portion 61 a at the tip of the stem 1, the head head ball 62 is held by the stem 61.

  The liner 63 and the socket 64 are formed of a hemispherical cup, and the liner 63 is disposed on the inner surface of the socket 64. The head ball 62 is attached to the liner 63 in a state in which the head ball 62 can swing on the inner surface of the liner 63.

<5-2. Artificial hip joint material>
The material of the artificial hip joint 6 is <1-3. The material is the same as the material of the angled plate 1 described in <Material of the angled plate><1-3. The description of the material of the angled plate> can also be applied to the artificial hip joint 6.

  In addition, the stem 61, the head ball 62, and the socket 64 of the artificial hip joint 6 are <1-3. The liner 63 may be formed of a polymer such as polyethylene or polyether ether ketone, for example. Further, the surface of the liner 63 may be surface-treated with MPC polymer. The MPC polymer refers to a polymer of 2-methacryloyloxyethyl phosphorylcholine (MPC) having a phospholipid polar group (phosphorylcholine group) and a methacryloyl group in the molecule. The liner 63 may be made of, for example, 64 titanium (for example, Ti-6Al-4V) or a Co—Cr—Mo alloy. Thereby, the wear between the head ball 62 and the liner 63 can be reduced.

<6. Other Embodiments>
Examples of implants according to other embodiments include, for example, a clavicle plate used when the clavicle fractures, and a rib plate used when the rib fractures, but is not limited thereto. All implants used for other osteopaths are included in the present invention.

  Moreover, the implant of this invention is not limited to what is used for osteopathy. For example, all the implants used in each part of the living body including implants used in various living body operations including a bar placed under the skin used in funnel chest surgery by the submuscular eggplant method are also included in the present invention.

  Furthermore, the implant according to the present invention, for example, is a head that holds each of the heads of two screw members that are screwed into a fractured portion or the like in a slidable or slidable or freely movable manner. It may be a part holding member. The head holding member restricts the movement of the other screw member by the movement of the one screw member. Thereby, it can prevent that the two screw members screwed into the fracture location etc. remove | deviate from a fracture location etc.

  Similarly, the above-described implant is preferably provided with at least a part of an elastically deformable portion that can be elastically deformed. Moreover, it is preferable that at least a part of the implant as described above is formed of a material having a reasonably low elastic limit. When at least a part of the implant as described above is formed of a material having a reasonably low elasticity limit, at least a part of the implant as described above can be easily plastically deformed.

  Moreover, the material of the above implants is <1-3. The material is the same as the material of the angled plate 1 described in <Material of the angled plate> <1-3. The explanation for the material of the square plate> is applicable to the above-described implant.

<7. Manufacturing method>
Next, an example of a method for manufacturing an implant in the embodiment of the present invention will be described with reference to FIG.

  First, a deformation process (hereinafter referred to as a first deformation process) is performed on one ingot of a titanium tantalum alloy containing tin (Sn) (S100). Thereby, the processing rate of one ingot changes. As the first deformation processing, for example, hot processing is given as an example. However, the first deformation processing is not limited to this, and may be processing related to other deformation processing. The hot working process is a plastic working performed by heating a metal to a recrystallization temperature or higher. Examples of plastic working include rolling, stretching, drawing, and the like, but are not limited to these, and other plastic working may be used.

  Next, a process for deforming the intermediate body of the implant formed by performing the first deformation process on the one ingot (hereinafter referred to as the second deformation process) different from the first deformation process. (Referred to as processing) (S101). The second deformation process is a so-called molding process, and the external shape of the implant is formed by the second deformation process. Further, the processing rate of the intermediate body of the implant is changed by the second deformation processing. Examples of the second deformation processing include, for example, cold processing (bending processing, drawing processing, press processing, forging, rolling processing, extrusion processing, drawing processing, etc.) and cutting processing, but are not limited thereto. It may not be a thing but the process regarding the deformation process regarding other shaping | molding. Note that the cold working process is a process performed at room temperature or below the recrystallization temperature of the material. Examples of the processing in the cold processing include, but are not limited to, various processes such as bending, drawing, cutting, pressing, rolling, forging, extrusion, and drawing. Other processing may be used.

  The first deformation process or the second deformation process may be performed on the entire one ingot or the entire intermediate body of the implant, respectively, or may be performed on a part of one ingot or a part of the intermediate body of the implant. You may do it for. The first deformation processing and the second deformation processing are each performed by deforming a part of one ingot or a part of the intermediate body of the implant until reaching a specific processing rate, and at least one of the remaining one ingot. It may be an aspect in which at least a part of the remaining part or the intermediate of the implant is deformed until reaching a processing rate (high processing rate or low processing rate) different from the specific processing rate.

  As described with reference to FIG. 5, the Young's modulus of the ingot can be changed low by changing the processing rate of the ingot high in the first deformation processing and the second deformation processing. For this reason, in any case, the Young's modulus of the portion where the processing rate of one ingot is high is low. And the part with a high processing rate should just be used as an elastic deformation part in an implant among one ingot.

  Next, the intermediate body of the implant subjected to the second deformation process is subjected to a heat treatment as necessary (step S102). The heat treatment may be performed on the entire intermediate body of the implant that has been subjected to the second deformation process, or only at a desired location of the intermediate body of the implant that has been subjected to the second deformation process. You may provide the part (hardening part) which raised hardness rather than the other part in the intermediate body. In addition, you may perform the heat processing in step S102 before and after the 1st deformation process process in step S100. That is, the heat treatment in step S102 may be performed on either one ingot before step S100 or an intermediate of the implant after step S100.

  Examples of the heat treatment include solution treatment and aging treatment. The solution treatment is a heat treatment for heating and dissolving the precipitate in the solid solution to obtain a single-phase structure of β phase. When a solution treatment is performed on the α + β alloy, a β phase structure can be obtained while leaving the α phase. The aging treatment is a heat treatment for heating to precipitate a precipitate (α phase) in the β phase. Each of the above solution treatment and aging treatment is a separate treatment, and each may be carried out separately at any timing from before step S100 to after step S101. include.

  Next, final machining is performed on the intermediate body of the implant that has undergone the above steps (S103). Thereby, an implant is completed. Examples of the final machining include, but are not limited to, polishing the surface of the implant intermediate, removing burrs from the implant intermediate, and making a hole through which the screw member passes. All final machining of other products is included in the present invention.

  In the above manufacturing process, when the first deformation processing and the second deformation processing are performed so that a different processing rate is given to each part for one ingot, each ingot has various Young's moduli. The parts are mixed. In this case, an implant in which the degree of elastic deformation is changed can be generated for each portion constituting the implant. For example, it is preferable that the portion of the implant component where the elastic deformation is most easily made is constituted by a portion having a higher processing rate in the entire implant. As described above, by controlling the processing rate with respect to one ingot or an intermediate body of an implant, an ideal implant in which rigidity and Young's modulus are changed for each part can be manufactured.

  Moreover, you may form an oxide film in the intermediate body of one ingot or an implant in any step of the said manufacturing process (oxide film formation process). When the oxide film is formed, the oxide film functions as a protective film and improves the corrosion resistance of the implant.

  Next, an example of an implant manufacturing method according to another embodiment of the present invention will be described with reference to FIG. In the implant manufacturing method according to the present embodiment, the first part of the implant is formed from the first ingot, the second part of the implant is formed from the second ingot, and the first part of the implant and the second part of the implant are formed. In combination with the premise that a completed implant is formed.

  First, a first deformation process (hereinafter referred to as a first ingot first deformation process) is performed on the first ingot of a titanium tantalum alloy containing tin (Sn) (S110). Further, a first deformation process (hereinafter referred to as a second ingot first deformation process) is performed on the second ingot of the titanium tantalum alloy containing tin (Sn) (S111).

  Next, with respect to the first intermediate body of the implant formed by subjecting the first ingot to the first deformation processing, the second deformation processing (hereinafter referred to as the first intermediate second deformation processing) Is called) (S112). Further, a second deformation processing (hereinafter referred to as a second intermediate second deformation processing) is performed on the second intermediate of the implant formed by performing the first deformation processing on the second ingot. ) Is performed (S113). As described above, the second deformation process is a so-called molding process, and the external shape of the first part and the second part of the implant is formed by the second deformation process.

  The first ingot first deformation processing may be performed on the entire first ingot or a part of the first ingot. In the first ingot first deformation processing, a part of the first ingot is changed to a specific processing rate, and at least a part of the first ingot is processed at a processing rate different from the specific processing rate (high). It may be a mode of deformation to a processing rate or a low processing rate. Similarly, you may perform a 2nd ingot 1st deformation process with respect to the whole 2nd ingot or a part of 2nd ingot. In the second ingot first deformation processing, a part of the second ingot is changed to a specific processing rate, and at least a part of the second ingot is processed at a processing rate different from the specific processing rate (high). It may be a mode of deformation to a processing rate or a low processing rate. Moreover, you may perform a 1st intermediate body 2nd deformation process with respect to the 1st intermediate body whole or a part of 1st intermediate body. Further, the first intermediate body second deformation processing process changes a part of the first intermediate to a specific processing rate, and at least a part of the remaining of the first intermediate is different from the specific processing rate. It may be a mode in which it is deformed to a rate (high processing rate or low processing rate). In addition, the second intermediate body second deformation processing may be performed on the entire second intermediate body or a part of the second intermediate body. In the second intermediate body second deformation processing, a part of the second intermediate is changed to a specific processing rate, and at least a part of the second intermediate is processed differently from the specific processing rate. It may be a mode in which it is deformed to a rate (high processing rate or low processing rate).

  In any case, the Young's modulus of the portion where the processing rate is increased is lower than before the processing rate is increased. As described above, the implant of the present invention may partially include an elastically deformable portion. Any portion of the first intermediate body or the second intermediate body with the increased processing rate may be used as an elastic deformation portion of the implant as appropriate. Note that the processing rate of the elastically deformable portion of the implant may vary depending on the degree of elastic deformation required in the implant.

  Next, heat treatment is performed on the first intermediate body or the second intermediate body of the implant as necessary (step S114). The heat treatment is the same as the embodiment described with reference to FIG. 16 and has already been described, and thus the description thereof is omitted. Moreover, you may perform heat processing to the whole 1st intermediate body of an implant, or its part, or the whole 2nd intermediate body of an implant, or its part. Thereby, the hardening part which raised hardness rather than the other part in the 1st intermediate body or the 2nd intermediate body can be provided.

  Further, the heat treatment is not limited to one performed immediately after step S112 and step S113, and may be performed before or after any step. That is, the heat treatment may be performed in a process before steps S112 and S113, or may be performed in a process after the final machining process in step S115.

  Next, final machining is performed on the first intermediate body or the second intermediate body of the implant that has undergone the above steps (S115). This completes the first or second part of the implant. The final machining is the same as the embodiment described with reference to FIG. 16 and has already been described. As described above, the first part and the second part of the implant are assembled (S116) to complete the implant.

  Further, an oxide film may be formed on the surface of the first ingot, the second ingot, the first intermediate, or the second intermediate at any stage of the manufacturing process (oxide film forming process). ). When the oxide film is formed, the oxide film functions as a protective film, and finally improves the corrosion resistance of the implant.

  The present invention includes all methods for producing implants by appropriately selecting any one of the processes described above and combining them.

  In the manufacturing process described above, the portion of the implant component that is desired to be most easily elastically deformed is constituted by a portion having a higher processing rate in the first intermediate body or the second intermediate body of the implant. It is preferable to do. If it does as mentioned above, the ideal implant which changed rigidity and Young's modulus for every part can be manufactured by control of the processing rate to the 1st intermediate body or the 2nd intermediate body of an implant.

  In the implant manufacturing method shown in FIGS. 16 and 17, the Young's modulus is controlled by performing the first deformation processing, the second deformation processing, and the heat treatment on the ingot. An example of a specific mode of controlling the Young's modulus will be described below.

  For example, when the square plate 1 shown in FIG. 1 is manufactured, when the bone auxiliary plate portion 10 and the blade portion 11 are formed by bending (second deformation processing), bending processing (second deformation processing) is performed. The Young's modulus of the part decreases. In this case, the Young's modulus is controlled by bending (second deformation processing).

  Further, as the holding time of the heat treatment for the titanium tantalum-based alloy becomes longer, the Young's modulus of the titanium tantalum-based alloy changes so as to increase as shown in FIG. In addition to the second deformation process, or in place of the bending process (second deformation process), the Young's modulus may be controlled by heat treatment.

  Next, an example of an implant manufacturing method according to another embodiment of the present invention will be described with reference to FIG. First, hot working is performed on one or more ingots of a titanium tantalum alloy containing tin (Sn) (S120). After hot working, the one or more ingots become the intermediate of the implant.

  Specifically, in the hot working process in step S120, one or a plurality of ingots are heated to a predetermined temperature, and the one or a plurality of ingots are formed into a plate material having a predetermined thickness or a bar material having a predetermined diameter. . That is, a plate material and a bar material are produced as an intermediate body of an implant through hot processing. In addition, when one or a plurality of ingots are heated to a predetermined temperature in the hot working process, it may be possible to obtain the same effect as when a solution treatment is performed on one or a plurality of ingots.

  Next, a cold working process is performed with respect to the intermediate body of the implant after a hot working process (S121). Examples of the process in the cold working process include various processes such as a bending process, a cutting process, a press process, a rolling process, and a forging process, but the present invention is not limited to these, and other processes may be used. . The cold working process in step S121 corresponds to a so-called molding process, and the appearance shape of the implant is formed by the cold working process in step S121. Further, the processing rate of the intermediate body of the implant may be controlled by cold processing.

  Next, heat treatment is performed on the intermediate body of the implant subjected to the cold working process (step S122). There are various forms of heat treatment here. For example, an aging treatment may be performed as a heat treatment on the entire implant intermediate subjected to the cold working treatment (S123). In this case, the hardness of the intermediate of the implant increases as a whole. When final machining is performed on the intermediate body of the implant that has undergone the aging treatment (S124), the implant is completed.

  Further, for example, a solution treatment may be performed as a heat treatment on the intermediate of the implant subjected to the cold working (S125). When the solution treatment is performed, a precipitate that precipitates in a titanium tantalum-based alloy containing tin (Sn) constituting the intermediate of the implant dissolves in the solid solution.

  After the solution treatment, for example, cold working (partial cold working) is performed on a part of the implant intermediate (S126). Thereby, the processing rate of a part of intermediate body of an implant can be changed. In addition, the aspect of change of a part of the intermediate part of the implant includes various aspects. For example, a mode in which the processing rate continuously changes along the length direction of the intermediate body of the implant, a mode in which the processing rate changes discontinuously along the length direction of the intermediate body of the implant, and the like can be given as examples. .

  Further, after the solution treatment, for example, an aging treatment (partial aging treatment) may be performed on a part of the intermediate of the implant (S127). Thereby, the hardness of a part of the intermediate body of the implant can be increased more than the other part.

  When final machining is performed on the intermediate body of the implant that has undergone the partial cold working process in step S126 or the partial aging process in step S127 (S124), the implant is completed.

  In addition, the implant of this invention and the manufacturing method of an implant are not limited to above-described embodiment, Of course, various changes can be added within the range which does not deviate from the summary of this invention.

DESCRIPTION OF SYMBOLS 1 Angled plate 2 Epiphyseal plate 3 Intramedullary nail 4 Nail 5 Lag screw 6 Hip prosthesis 61 Stem 62 Bone head ball 63 Liner 64 Socket 10, 20 Bone auxiliary plate part 11 Blade part 12, 22, 41 Screw member 21 End part plate Part 13, 23, 24, 42 Hole 30 Linear part 12a, 31 Head 43 Through-hole 51 Screw groove

Claims (23)

At least a portion comprising an alloy containing titanium, tantalum and tin,
The alloy contains 15 atomic% to 27 atomic% tantalum and 1 atomic% to 8 atomic% tin when the whole is 100 atomic%, and the balance is composed of titanium and inevitable impurities. And
Implant. It is provided with an elastically deformable portion that can be elastically deformed at least in part,
The implant according to claim 1. The elastically deformable portion is constituted by a portion having a higher processing rate than other portions,
The implant according to claim 2. It has a hardened part with higher hardness than other parts,
The hardened part is formed by heat treatment,
The implant according to claim 1. An aging treatment is performed on at least a part of the alloy,
The implant according to claim 1. The retention time of the alloy in the aging treatment is within 30 hours,
The implant according to claim 5. Characterized by reducing bones,
The implant according to claim 1. Comprising a part attached to the outer peripheral surface of the bone,
The portion attached to the outer peripheral surface of the bone is formed in a plate shape,
The implant according to claim 7. The part attached to the outer peripheral surface of the bone is fixed to the outer peripheral surface of the bone with a screw member,
The implant according to claim 8. It is configured to include a part that is attached to the inside of the bone,
The implant according to claim 7. It is configured to include a portion that penetrates inside the broken bones,
The implant according to claim 7. The portion that penetrates inside the broken bones is formed in a screw shape,
The implant of claim 11. At least a part is formed in a screw shape,
The implant according to claim 7. At least a part is formed in a bar shape,
The implant according to claim 7. Producing an implant using a material comprising an alloy containing titanium, tantalum and tin,
Implant manufacturing method. Comprising a deformation processing step of deforming at least a part of the material,
The manufacturing method of the implant of Claim 15. Characterized in that it comprises an aging treatment step of aging treatment on at least a part of the material, or at least a part of an intermediate formed in the manufacturing process of the implant,
The manufacturing method of the implant of Claim 15. The retention time of the alloy in the aging treatment is within 30 hours,
The manufacturing method of the implant of Claim 17. Characterized in that it comprises a solution treatment step of performing a solution treatment on at least a part of the material or at least a part of an intermediate formed in the manufacturing process of the implant.
The manufacturing method of the implant of Claim 15. A solution treatment step of performing a solution treatment on at least a part of the material or at least a part of an intermediate formed in the manufacturing process of the implant,
The solution treatment step is performed after the deformation processing step,
The manufacturing method of the implant of Claim 16. In the deformation processing step, a part of the material is changed to a first processing rate, and at least a remaining part of the material is changed to a second processing rate higher than the first processing rate. To
The manufacturing method of the implant of Claim 16. The material consists of two ingots comprising an alloy containing titanium and tantalum,
The deformation processing step is
A first ingot deformation process step of performing a process of changing at least a part of one ingot to a first processing rate;
A second ingot deformation processing step for performing a process of changing at least a part of another ingot to a second processing rate higher than the first processing rate;
With
The implant is composed of at least a first portion and a second portion;
The first portion is formed from an ingot that has undergone the first ingot deformation processing step.
The second portion is formed from an ingot that has undergone the second ingot deformation processing step.
The manufacturing method of the implant of Claim 16. The implant is formed such that a portion whose processing rate is changed in the deformation processing step constitutes an elastically deformable portion that can be elastically deformed,
The manufacturing method of the implant of Claim 16.

Images