JP3011325B2 - Titanium wire for living body and method for producing the same - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a titanium wire for use in a living body, for example, for fastening a human bone, and a method of manufacturing the same.

[0002] Such a titanium wire is required to be able to be easily and firmly fastened during the operation and to have high safety in a living body.
An excellent titanium wire suitable for such a purpose is provided.

[0003]

2. Description of the Related Art In recent years, in the field of orthopedic surgery or oral surgery, implanting artificial bones, artificial roots, and the like into a living body has been performed. Especially when bone damage occurs
Implant artificial bone in the damaged area, or reinforce or fix until the bone recovers. In spine surgery and the like, bone transplantation and the like are performed.

In general, stainless steel and chromium-cobalt based materials are often used for such artificial bones or joint materials. However, there have been many reports that stainless steel has been associated with malignant tumors after artificial joint replacement, and the elution of toxic metal ions in vivo has recently been regarded as a problem.

[0005] Stainless steel is generally referred to as a corrosion-resistant material. However, the surface of the corrosion-resistant film (passive film) is partially destroyed due to scratches on the stainless steel itself during surgery or use. If the passive film regenerates rapidly, the oxygen partial pressure in the body is low, so the fabric is exposed for a long period of time, and metal ions such as nickel, which is a main additive element of stainless steel, may elute. There is also. It has been reported that metallic nickel itself has toxicity as an allergic or carcinogenic substance.

[0006] In addition to the above, as a metal to be buried in the body, a metal wire is used to fix or reinforce the bone or the bone and the artificial bone or the implanted bone. As the metal wire, a stainless steel wire is often used, taking advantage of its high strength. However, there is a danger that galvanic corrosion occurs between the above-mentioned metallic artificial bone and metal ions are more easily eluted. Due to the occurrence of such a problem, the following properties are required as a fastening wire for a living body.

Biocompatibility No cytotoxicity or no toxicity per se. No elution as metal ions. Good compatibility with living tissue. No carcinogenicity and no antigenicity. No metabolic abnormalities. Do not cause blood clotting or hemolysis

[0008] Mechanical properties: To have appropriate static strength and ductility. To have sufficient fatigue strength.

[0009]

Because of the above problems, the use of toxic metals or alloy materials containing them as a component has been avoided.

For these reasons, attention has been focused on titanium materials which are excellent in corrosion resistance and lighter as a material replacing stainless steel and chromium-cobalt materials.

This titanium material is roughly divided into pure titanium and titanium alloy. Pure titanium varies in strength depending on the amount of oxygen, and is defined in JIS standards as being divided into one to three types from those having a low oxygen amount.

On the other hand, titanium alloys include V, Mo, Fe, Cr
As β-stabilizing elements increase, a β-phase becomes present up to room temperature.
It is classified into three types, β-type and β-type. Among the titanium alloys, Ti-6Al-4V is known for medical use. It is defined in the American ASTM and ISO standards as a surgical implant material. However, since this alloy contains V, which is said to exhibit strong cytotoxicity when used alone, some researchers have pointed out the dangers. Is being done.

With respect to pure titanium, the impurity content of oxygen is 1500 ppm or less, nitrogen is 500 ppm or less,
Although it is 3000 ppm or less of iron and 130 ppm or less of hydrogen, it is considered that there is no particular concern about cytotoxicity due to such impurity content.

In any case, since the titanium material is clearly superior to other materials in characteristics, the use as a biomaterial and the research on new materials are rapidly increasing in recent years.

However, if the artificial bone and the fastening wire for a living body are used in the same place, the contact portion between the two is immersed in the body fluid in the living body, and there is a great risk of galvanic corrosion occurring. This is particularly noticeable when using dissimilar materials such as stainless steel. Therefore, when using pure titanium or a titanium alloy as an implant material for a living body such as an artificial bone, it is desirable to use the same type of titanium wire.

[0016] However, it is said that titanium material is inferior in mechanical strength and elongation as compared with stainless steel wire, and it has not yet been concluded whether titanium-based material is a material suitable as a fastening wire for living body. Is the current situation.

A particular problem with such a fastening wire for a living body is the fastening of the wire. When fixing a bone with a wire, it is general to perform twisting in general.However, the fastening by twisting can be tightly wound around the object so that it does not loosen, and during and after fastening It is necessary that the wire does not break even afterwards.

As such a fastening wire, one kind of JIS standard pure titanium or two kinds of J with increased strength by increasing oxygen.
The IS standard has been proposed and research reports have shown that it shows relatively good fastening properties. However, as shown above,
S-grade pure titanium has problems such as breaking with several twists or breaking with a gap left without being tightly wound around the object. Pure titanium has no problem with cytotoxicity, etc., but the fact remains that such unsolved problems remain.

In view of such problems, a method of fastening has been devised to improve the fastening method, and a mechanical fixing method by caulking has been proposed. However, a special tool for caulking is required in addition to many surgical tools, and There is a drawback that the fastening work is inevitably complicated, such as requiring a certain level of skill, and thus there is a face that cannot be said to be a fundamental solution.

[0020]

As a result of diligent tests and studies on the above-mentioned problems, the present inventors have found that the trace impurities contained in titanium are more strictly prepared, so that when the wires are fastened, they become loose. The present invention has found an excellent material that can be used as a fastening wire for living body without breakage or breakage.

That is, in the first aspect of the present invention, the gas components of 300 ppm or less of oxygen, 50 ppm or less of hydrogen,
The present invention relates to a fastening titanium wire for a living body, which is 00 ppm or less, carbon is 400 ppm or less, impurities other than gas components are 100 ppm or less, and the balance is titanium.

Next, a second aspect of the present invention is to provide a gas component having an oxygen content limited to a preferred range of 200 ppm or less of oxygen, 50 ppm or less of hydrogen, 200 ppm or less of nitrogen, 400 ppm or less of carbon, and 100% or less of impurities other than the gas component.
The present invention relates to a fastening titanium wire for a living body which is not more than ppm and the balance is titanium.

Next, a third aspect of the present invention relates to a gas component having an oxygen content of 100 p.p.m.
The present invention relates to a fastening titanium wire for a living body, which is pm or less, hydrogen is 50 ppm or less, nitrogen is 200 ppm or less, carbon is 400 ppm or less, impurities other than gas components are 100 ppm or less, and the balance is titanium.

Next, a fourth invention relates to the invention corresponding to each of the above 1 to 3, wherein the content of hydrogen is more preferably limited to 30 ppm or less.

Next, the fifth invention relates to the invention corresponding to each of the above-mentioned items 1 to 3, wherein the content of hydrogen is further restricted to 20 ppm or less.

Next, the sixth invention relates to the invention corresponding to each of the above-mentioned 1 to 5, wherein the content of nitrogen is more preferably limited to 100 ppm or less.

Next, the seventh invention relates to the invention corresponding to each of the above 1 to 5, wherein the nitrogen content is further restricted to 50 ppm or less.

Next, an eighth invention relates to the invention corresponding to each of the above-mentioned 1 to 5, wherein the nitrogen content is further restricted to 20 ppm or less.

Next, a ninth invention relates to the invention corresponding to each of the above 1 to 8, wherein the content of carbon is more preferably limited to 200 ppm or less.

Next, a tenth invention relates to the invention corresponding to each of the above-mentioned 1 to 8, wherein the content of carbon is further limited to 100 ppm or less.

Next, an eleventh invention relates to the invention corresponding to each of the above-mentioned 1 to 8, wherein the content of carbon is restricted to an even more preferable 50 ppm or less.

Next, a twelfth invention relates to the invention corresponding to each of the above-mentioned 1 to 11, wherein impurities other than gas components are limited to 50 ppm or less.

Next, a thirteenth invention relates to the invention corresponding to each of the above-mentioned 1 to 12, wherein impurities other than gas components are limited to 20 ppm or less.

Next, according to a fourteenth aspect, the average crystal grain size is 5 μm.
The present invention relates to the invention corresponding to each of the above items 1 to 13 having a size of m to 150 μm.

Further, a fifteenth aspect of the present invention relates to an optimal method for obtaining a titanium wire for a living body, which is a temperature range of 400 ° C. to 900 ° C., preferably 500 ° C. after final cold drawing.
~ 700 ° C, more preferably 550 ° C ~ 650
1 to 14 characterized by annealing in a temperature range of ℃.
The present invention relates to an invention of a method for manufacturing a fastening titanium wire for a living body corresponding to each of the above. (Here, the number of inventions counted in the section of “Means for Solving the Problems” is omitted for convenience of explanation, and the actual number of inventions is a combination thereof. To do.)

[0036]

The details of the present invention and its operation will be described below. First, the reasons for limitation of oxygen and the like contained in the living body fastening titanium wire will be described in detail.

Oxygen (O): In the present invention, oxygen is 30
0 ppm or less. When oxygen exceeds 300 ppm,
The ductility is poor and the minimum required elongation is less than 30%.

Further, as described later, at the time of torsion fastening,
The gap is widened without winding up to the root of the fixed object, or the gap is broken before winding is completed even if it is forcibly wound (breakage of type B in an explanatory diagram described later). In some cases, a break occurs at a transition portion with a single wire instead of a twisted portion (a breakage of type C in an explanatory diagram described later), which is unsuitable as a living body fastening wire.

When such a wire is used, in addition to the fact that the fastening is not sufficient, breakage is apt to occur particularly during the operation, so that the operation must be performed again and it takes time, for example.

This oxygen is preferably less than 200 ppm,
More preferably, it is 100 ppm or less. As a result, as shown in the test results described later, the titanium wire has sufficient ductility (elongation) to be wound around the root of the object to be fixed, and is suitable as a living body fastening titanium wire.

Hydrogen (H): In the present invention, hydrogen is 50
ppm or less. Hydrogen affects ductility in smaller amounts than oxygen. When the hydrogen content exceeds 50 ppm, the ductility rapidly deteriorates even if other impurities are reduced, and the minimum required elongation becomes less than 30%.

Also, similarly to the above-mentioned oxygen, at the time of torsion fastening as described later, the gap is widened without winding up to the root of the fixed object, or the winding is performed even if it is forcibly wound. It breaks before it is completed (type B breakage in an explanatory diagram described later). In some cases, a break occurs at a transition portion with a single wire instead of a twisted portion (a breakage of type C in an explanatory diagram described later), which is unsuitable as a living body fastening wire.

When such a wire is used, in addition to the fact that the fastening is not sufficient, breakage is liable to occur particularly during the operation, so that the operation must be performed again and it takes time. This hydrogen is preferably 30 pp
m, more preferably 20 ppm or less.

As described above, as shown in the test results described later, it has sufficient ductility (elongation) to be wound around the root of the object to be fixed, and is suitable as a fastening titanium wire for living bodies.

Nitrogen (N): In the present invention, nitrogen is 20
0 ppm or less. Nitrogen has a ductility reduction of about 1.5 times that of oxygen. When nitrogen exceeds 200 ppm, ductility rapidly deteriorates even if other impurities are reduced,
The minimum required elongation is less than 30%.

Also, similarly to the above-mentioned oxygen, at the time of torsion fastening as described later, the gap is widened without winding up to the root of the fixed object, or the winding is forcibly wound. It breaks before it is completed (type B breakage in an explanatory diagram described later). In some cases, a break occurs at a transition portion with a single wire instead of a twisted portion (a breakage of type C in an explanatory diagram described later), which is unsuitable as a living body fastening wire.

When such a wire is used, in addition to the fact that the fastening is not sufficient, breakage is apt to occur particularly during the operation, so that the operation must be performed again and it takes time, for example.

This nitrogen is preferably less than 100 ppm,
More preferably, it is 50 ppm or less. More preferably, it is 20 ppm or less. As described above, as shown in the test results described later, the wire has sufficient ductility (elongation) to be wound around the root of the object to be fixed, and is suitable as a living body fastening titanium wire.

Carbon (C): In the present invention, carbon is 40
0 ppm or less. Carbon exists as an interstitial solid solution element in Ti and has the function of increasing the strength of Ti.
Conversely, this results in about 0.75 times lower ductility at the same concentration than oxygen.

When the content of carbon exceeds 400 ppm, the ductility rapidly deteriorates even if other impurities are reduced, and the minimum required elongation becomes less than 30%. Further, similarly to the above-described oxygen, at the time of torsion fastening as described later, the gap is wide open without winding up to the root of the fixed object, or the winding is not completed even if it is forcibly wound. (The type B in the explanatory diagram described later). In some cases, a break occurs at a transition portion with a single wire instead of a twisted portion (a breakage of type C in an explanatory diagram described later), which is unsuitable as a living body fastening wire.

When such a wire is used, in addition to the fact that the fastening is not sufficient, breakage is liable to occur particularly during the operation, so that the operation must be performed again and it takes a long time.

This carbon is preferably less than 200 ppm,
More preferably, it is 100 ppm or less. More preferably, it is 50 ppm or less. As described above, as shown in the test results described later, the wire has sufficient ductility (elongation) to be wound around the root of the object to be fixed, and is suitable as a living body fastening titanium wire.

Impurities other than the above gas components: In the present invention, impurities other than the above gas components are set to 100 ppm or less.

When the amount of impurities other than gas components exceeds a certain amount, ductility rapidly deteriorates, and the minimum required elongation becomes less than 30%. Then, similarly to the above-described oxygen, at the time of torsion fastening as described below, the gap is wide open without winding up to the root of the fixed object, or the winding is not completed even if it is forcibly wound. (The type B in the explanatory diagram described later). In some cases, a break occurs at a transition portion with a single wire instead of a twisted portion (a breakage of type C in an explanatory diagram described later), which is unsuitable as a living body fastening wire.

When such a wire is used, in addition to being insufficiently fastened, breakage is liable to occur particularly during the operation, so that the operation must be performed again and it takes time, for example. The impurities other than the gas components are preferably at most 50 ppm, more preferably at most 20 ppm.

As described above, as shown in the test results described later, it has sufficient ductility (elongation) to be wound around the root of the object to be fixed, and is suitable as a fastening titanium wire for a living body.

Description of Tensile Strength and Yield Strength (Yield Stress) of the Wire In the above, the limitation of impurities in the living body fastening titanium wire has been described. However, the living body fastening wire is sufficient for fixing or fastening bone. Tensile strength and strength are required. It is desirable to have a tensile strength and a proof stress of 180 MPa and 70 MPa or more, respectively.

The presence of some of the impurities described above is rather preferred, as the impurities described above will generally be more or less likely to increase the strength of titanium. However, the presence of excess tends to lose the properties of high ductility and pliability required for biomedical fastening wires. If the strength is increased at the expense of ductility, the risk of breaking the fastening wire arises and must be avoided.

As described above, high ductility is indispensable for a fastening wire for a living body. Generally, if the tensile strength and the proof strength are 180 MPa and 70 MPa or more, respectively, there is no practical inconvenience and it is suitable as a living body fastening wire.

When the strength is to be increased as much as possible when the bone is used for joining a bone which is subjected to a large load, it is necessary to increase the wire diameter or to knit several wires to form a fastening wire having increased strength. Therefore, such a method can be adopted as necessary. The fastening titanium wire for living body of the present invention sufficiently satisfies the above conditions.

Next, the average crystal grain size and the like will be described. In the present invention, the average grain size is 5 μm to 150 μm.
m is desirable. The smaller the crystal grain size, the higher the toughness. However, in practice, the one with a grain size of less than 5 μm is difficult to manufacture, and even if it can be manufactured, some of the strain remains and the ductility value decreases.
On the other hand, when the average crystal grain size is large, especially when it exceeds 150 μm, the number of crystal grains becomes small with respect to the wire diameter, and the ductility is locally deteriorated.

Next, details of the manufacturing method will be described.
A titanium ingot is prepared by melting and casting a titanium material for which a predetermined component has been prepared. The gas components oxygen, nitrogen,
In order to remove impurities such as hydrogen and carbon to a predetermined amount or less, a vacuum arc melting method, an electron beam melting method, or the like can be used. After forging the obtained titanium ingot as necessary, groove rolling, swaging, and wire drawing are performed, and for example, φ1.7, φ1.0, φ0.8, φ
It is made into a wire having a predetermined diameter such as 0.4. The diameter of the wire is adjusted by appropriately changing the diameter of the die and performing wire drawing. The area reduction rate is about 30 to 90%.

In the course of this processing step, intermediate annealing (400 to
(In a temperature range of 900 ° C., preferably in a temperature range of 500 to 700 ° C., more preferably in a temperature range of 550 to 650 ° C., for about 10 seconds to 5 hours).

In place of the above-described manufacturing process, a plate-like material obtained by rolling is cut into a square rod, and the corners of the square bar are cut off with a grinder or the like, followed by swaging and drawing. You can also.

After the final processing, a temperature range of 400 to 900 ° C., preferably 500 to 700 ° C., more preferably 5 to 700 ° C.
The final annealing is performed in a temperature range of 50 to 650 ° C. for about 5 seconds to 5 hours. A predetermined crystal grain (for example, an average crystal grain size of 5 μm to 150 μm) is prepared through the above processing and annealing. Intermediate annealing and final annealing can be used either continuously or batchwise. Thus, a titanium wire having a predetermined diameter is manufactured.

The fastening titanium wire for a living body of the present invention described above is used for fastening a human bone or an artificial bone in a living body, and has sufficient ductility (elongation) to be wound around the root of an object to be fixed. It can be easily and firmly fastened during surgery, and has excellent characteristics of high in-vivo safety.

[0067]

Examples and Comparative Examples Hereinafter, the present invention will be described with reference to Examples (compared with Comparative Examples). Titanium ingots were prepared by melting and casting the titanium materials for which the components had been prepared. An electron beam melting method was used to remove impurities such as oxygen, nitrogen, hydrogen, and carbon as gas components.

After forging the obtained titanium ingot,
Groove roll rolling, swaging, wire drawing, φ
Wires having diameters of 1.0 and φ0.8 were produced. The area reduction rate is about 30 to 90%. During this processing step,
Intermediate annealing was performed in a temperature range of 400 to 900 ° C. After the final processing, final annealing was performed in a temperature range of 400 to 900 ° C. The average crystal grain size was 5 μm to 150 μm.

Table 1 shows the component analysis values of the test materials of the titanium wire prepared as described above. The values shown in the sample numbers (1 to 19) in Table 1 are the average values of 20 samples. Component analysis values are rounded to the nearest single digit.

In addition, instead of the above-described manufacturing process, the plate-shaped material obtained by rolling is cut into a square rod, and the corners of the square bar are cut off with a grinder or the like, and then swaged and drawn. Was performed to produce a titanium wire, but for those whose component analysis values fall within the scope of the present invention,
There was no difference in characteristics.

Further, due to differences in the annealing temperature range of 500 ° C. to 700 ° C. and 550 ° C. to 650 ° C., and the average crystal grain size, those which depart from the numerical range described as “more preferable range” in the description of the present invention are as follows: There is a tendency for the dispersion to be slightly larger than the characteristic value in the “more preferable range”, but there is no particular difference in the characteristic when the component analysis value falls within the range of the present invention.

For comparison, a similar manufacturing process was performed to produce a titanium wire in which impurities were prepared.

Table 1 also shows the component analysis values of the test materials. The values shown in the sample numbers (20 to 30) in Table 1 are average values of 20 samples as in the example of the present invention. Similarly, the component analysis values are obtained by rounding one digit.

[0074]

[Table 1]

Next, the following test was performed using each test material. (1) Tensile test (measurement of elongation) Distance between gauge points: 70 mm, tensile speed 10 mm / mi
A tensile test was performed on two types of wires having n and a diameter between the reference points: 1.0 mm and 0.8 mm.

(2) Twisting (Torsion) Test A jig to be wound: a round bar fixing jig having a diameter of 20 mm, the number of rotations: 60 rpm, and two kinds of wires having a wire diameter of 1.0 mm and 0.8 mm were twisted. (Torsion) test.

The results of the above tensile test (measurement of elongation) are shown in Table 1 and FIGS. As is evident from Table 1, all of Samples 1 to 19 of the present invention have an elongation of 30% or more and exhibit good ductility. In particular, ductility is higher when the gas components are oxygen 200 ppm or less, hydrogen 30 ppm or less, nitrogen 100 ppm or less, carbon 100 ppm or less, and impurities other than gas components 50 ppm or less. More preferably, oxygen is 100 ppm or less, hydrogen is 20 ppm or less, nitrogen is 20 ppm or less, carbon is 50 ppm or less, and impurities other than gas components are 20 ppm or less, all of which exhibit extremely high ductility.

On the other hand, sample 2 presented as a comparative example
In the case of 0 to 30, the elongation was less than 30% and the ductility was extremely poor. Samples 20 to 30 of these comparative examples were all 300 ppm of oxygen and 5 ppm of hydrogen.
0 ppm, 200 ppm of nitrogen, 400 ppm of carbon, and impurities other than gas components exceeding 100 ppm, which are unsuitable materials for fastening titanium wires for living bodies.

FIG. 1 shows samples 1, 2, 3, 4 and Comparative Example 2.
0, 21 and 22 show changes in elongation depending on the oxygen content.

FIG. 2 shows Samples 1, 5, 6, 7 and Comparative Example 2.
3 and 24 show changes in elongation depending on the carbon content.

FIG. 3 shows Samples 1, 8, 9, and 10 and Comparative Examples 25 and 26, showing the change in elongation depending on the nitrogen content.

FIG. 4 shows Samples 1, 11, 12, and 13 and Comparative Examples 27 and 28, showing changes in elongation depending on the hydrogen content.

FIG. 5 shows Samples 1, 14, 15, and 16 and Comparative Examples 29 and 30, showing changes in elongation due to the content of impurities other than gas components. In each case, it is obvious that the elongation of the example of the present invention is better than that of the comparative example.

The tensile strength and proof stress in the tensile test were 180 MPa and 70 MPa, respectively.
Having the above, there is no practical inconvenience and it is suitable as a living body fastening wire.

[0085]

[Table 2]

The results of the torsion test are shown in Tables 1 and 2, FIGS. 6 to 10, and FIG. 11 shows the classification of the fracture modes.

As shown in FIG. 11, a 20 mm diameter round bar fixing jig was subjected to a torsion (torsion) test at a rotational speed of 60 r.
It shows the state wound by pm. Type A shows a state in which the jig is wound neatly to the base of the jig with little gap (less than 1.0 mm gap).

When the fracture occurs (by excessive winding), the fracture form is in the middle of the twisted portion, that is, the place where the processing strain is concentrated, and shows a favorable fracture form.

On the other hand, in the case of type B, the jig is broken when it cannot be wound up to the base of the jig (a gap of 1.0 mm or more). This occurs when the ductility of the wire is not sufficient. In this case, loosening occurs in the fastening.

Further, in the case of type C, breakage occurs at the transition between the winding portion and the single wire (elementary wire). This condition is completely unsuitable for a fastening wire.

As is clear from Table 2, in the samples 1 to 19 shown in the examples of the present invention, both the 1.0 mm diameter and the 0.8 mm diameter show the type A fracture mode, and almost no gap is formed. (The gap is less than 1.0 mm) This indicates that the jig can be wound neatly to the base.

The details of the gap for winding around the jig are shown in Table 1 and FIGS. As is clear from these, the gap was 1.0 m in each of the samples 1 to 19.
m, and the better the ductility, the better. Some samples have a gap of 0 and are even wound tightly to the root.

On the other hand, the samples 20 to 30 of the comparative examples show the broken form of the type B or the type C, and as shown in Table 1 and FIGS. (With a gap of 1.0 mm or more), or breakage occurs at the transition between the wound portion and the single wire (elementary wire). These are unsuitable as fastening titanium wires for living bodies, and there is a risk that the wires may break during or after surgery or that the fastening may not be sufficient.

[0094]

As described above, titanium is known to have good fatigue strength, tensile strength, corrosion resistance and biocompatibility. It is a solution to the problem. Moreover, no toxic or soluble constituent elements are used in this solution.

As described above, the fastening titanium wire for a living body of the present invention is used for fastening a human bone or an artificial bone in a living body, and has sufficient ductility to be wound up to the root of an object to be fixed. (Elongation), can be easily and firmly fastened during surgery, and have excellent properties that are highly safe in vivo. In particular, it exerts an excellent function in fixing bone grafts and the like.

[Brief description of the drawings]

FIG. 1 is an explanatory diagram of a change in elongation due to an oxygen content.

FIG. 2 is an explanatory diagram of a change in elongation according to a carbon content.

FIG. 3 is an explanatory diagram of a change in elongation depending on a nitrogen content.

FIG. 4 is an explanatory diagram of a change in elongation due to a hydrogen content.

FIG. 5 is an explanatory diagram of a change in elongation due to the content of impurities other than gas components.

FIG. 6 is an explanatory diagram of a change in a gap depending on an oxygen content.

FIG. 7 is an explanatory diagram of a change in a gap depending on a carbon content.

FIG. 8 is an explanatory diagram of a change in a gap depending on a nitrogen content.

FIG. 9 is an explanatory diagram of a change in a gap due to a hydrogen content.

FIG. 10 shows a change in a gap due to an impurity content other than a gas component.

FIG. 11 is an explanatory diagram showing a classification of a fracture mode.

──────────────────────────────────────────────────続 き Continuation of the front page (56) References JP-A-2-211164 (JP, A) (58) Fields investigated (Int. Cl. ⁷ , DB name) A61L 17/00-31/00

Claims (30)

(57) [Claims] Claims: 1. An oxygen gas component of 300 ppm or less,
Hydrogen 50 ppm or less, nitrogen 200 ppm or less, carbon 40
0 ppm or less, and impurities other than gas components are 100 pp
m, a titanium fastening wire for a living body, the remainder being titanium. 2. A gas component of oxygen of 200 ppm or less,
Hydrogen 50 ppm or less, nitrogen 200 ppm or less, carbon 40
0 ppm or less, and impurities other than gas components are 100 pp
m, a titanium fastening wire for a living body, the remainder being titanium. 3. Oxygen as a gas component is 100 ppm or less,
Hydrogen 50 ppm or less, nitrogen 200 ppm or less, carbon 40
0 ppm or less, and impurities other than gas components are 100 pp
m, a titanium fastening wire for a living body, the remainder being titanium. 4. The fastening titanium wire for a living body according to claim 1, wherein the hydrogen content is 30 ppm or less. 5. The fastening titanium wire for a living body according to claim 1, wherein hydrogen is 20 ppm or less. 6. The fastening titanium wire for a living body according to claim 1, wherein the nitrogen content is 100 ppm or less. 7. The fastening titanium wire for a living body according to claim 1, wherein nitrogen is 50 ppm or less. 8. The fastening titanium wire for a living body according to claim 1, wherein the nitrogen is 20 ppm or less. 9. The living body fastening titanium wire according to claim 1, wherein the carbon content is 200 ppm or less. 10. The fastening titanium wire for a living body according to claim 1, wherein the carbon content is 100 ppm or less. 11. The fastening titanium wire for a living body according to claim 1, wherein the carbon content is 50 ppm or less. 12. The living body fastening titanium wire according to claim 1, wherein impurities other than gas components are 50 ppm or less. 13. The fastening titanium wire for a living body according to claim 1, wherein impurities other than gas components are 20 ppm or less. 14. The fastening titanium wire for a living body according to claim 1, wherein the average crystal grain size is 5 μm to 150 μm. 15. After the final cold drawing, at 400 ° C. to 90 ° C.
Annealing in a temperature range of 0 ° C. is a gas component of 300 ppm or less of oxygen, 50 ppm or less of hydrogen,
A method for producing a fastening titanium wire for a living body, which is 00 ppm or less, carbon is 400 ppm or less, impurities other than gas components are 100 ppm or less, and the balance is titanium. 16. After final cold drawing, 400 ° C. to 90 ° C.
Annealing in a temperature range of 0 ° C. is a gas component of 200 ppm or less of oxygen, 50 ppm or less of hydrogen,
A method for producing a fastening titanium wire for a living body, which is 00 ppm or less, carbon is 400 ppm or less, impurities other than gas components are 100 ppm or less, and the balance is titanium. 17. After final cold drawing, at 400 ° C. to 90 ° C.
Annealing in a temperature range of 0 ° C. is characterized by gas components of oxygen 100 ppm or less, hydrogen 50 ppm or less, nitrogen 2
A method for producing a fastening titanium wire for a living body, which is 00 ppm or less, carbon is 400 ppm or less, impurities other than gas components are 100 ppm or less, and the balance is titanium. 18. After the final cold drawing, at 500 ° C. to 70
Annealed in a temperature range of 0 ° C.
18. The method for producing a fastened titanium wire for living body according to any one of 17. 19. 550 ° C.-65 after final cold drawing
Annealed in a temperature range of 0 ° C.
18. The method for producing a fastened titanium wire for living body according to any one of 17. 20. The method according to claim 15, wherein the hydrogen content is 30 ppm or less. 21. The method according to claim 15, wherein the hydrogen content is 20 ppm or less. 22. The method according to claim 15, wherein the nitrogen content is 100 ppm or less. 23. The method according to claim 15, wherein nitrogen is 50 ppm or less. 24. The method according to claim 15, wherein the nitrogen content is 20 ppm or less. 25. The method according to claim 15, wherein the carbon content is 200 ppm or less. 26. The method according to claim 15, wherein the carbon content is 100 ppm or less. 27. The method for producing a living fastening titanium wire according to claim 15, wherein the carbon content is 50 ppm or less. 28. The method according to claim 15, wherein impurities other than gas components are 50 ppm or less. 29. The method according to claim 15, wherein impurities other than gas components are 20 ppm or less. 30. The method according to claim 15, wherein the average crystal grain diameter is 5 μm to 150 μm.