JP3641512B2 - Orthodontic wire and method for manufacturing the same - Google Patents
Orthodontic wire and method for manufacturing the same Download PDFInfo
- Publication number
- JP3641512B2 JP3641512B2 JP15818295A JP15818295A JP3641512B2 JP 3641512 B2 JP3641512 B2 JP 3641512B2 JP 15818295 A JP15818295 A JP 15818295A JP 15818295 A JP15818295 A JP 15818295A JP 3641512 B2 JP3641512 B2 JP 3641512B2
- Authority
- JP
- Japan
- Prior art keywords
- wire
- orthodontic
- manufacturing
- orthodontic wire
- treatment
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Lifetime
Links
Images
Description
【0001】
【産業上の利用分野】
本発明は歯並びを矯正する歯列矯正用ワイヤーに関するものであり、歯の矯正治療の最終段階において、わずかな歯の移動を制御して歯を固定するワイヤーとして使用する。
【0002】
【従来の技術】
歯並びの矯正治療においては、治療の段階に合わせて種々の歯列矯正用ワイヤーが使用される。歯を大きく移動させる初期の段階には、主に超弾性を有するNi−Ti合金のワイヤーが使用される。そしてわずかな歯の移動を制御して歯を固定する矯正治療の最終段階には、高い機械的強度(特に抗曲力)を有する合金のワイヤーが使用される。従来、この矯正治療最終段階で歯を固定するために使用する歯列矯正用ワイヤーとして、主に線径が0.4mm程度の熱処理をしたハイカーボンステンレス鋼製ワイヤーが使用されていた。
【0003】
【本発明が解決しようとする課題】
前記のハイカーボンステンレス鋼製ワイヤーは高い抗曲力を有しているが、
(1)耐食性が悪く錆びやすい。
(2)靭性に劣り曲げると破断しやすい。
(3)熱処理により生じた酸化被膜により表面が荒れてザラザラして滑り難く、わずかな歯の移動を制御するのに支障をきたす。
(4)ワイヤーにカールがついており、患者の歯並びの形に合わせてワイヤーを成形し難い。
等の課題を有していた。
【0004】
【課題を解決するための手段】
前記課題を解決するために、本発明においてワイヤーの材質を、高い機械的強度および優れた耐食性と強靭性を有するCo−Ni基合金とした。このCo−Ni基合金とは、例えば、特許第1374564号の合金を示すものである。この特許1374564号の合金とは、主成分がCo、Ni、Cr、Moで、組成は重量比でCr+Mo20〜40%、Ni20〜50%、Co25〜45%、Mn、Ti、Al、Fe各0.1〜5%、Nb0.1〜3%、Ce、Y、ミッシュメタルから選択される希土類元素1種または2種以上0.01〜1%から成る。この合金を用い、断面減少率で表される加工度60〜90%で冷間線引加工を行う。ここで加工度を60%以上としたのは、加工度がこれより低くなるとワイヤーに必要な機械的強度が得られないからであり、加工度を90%以下としたのは、加工度がこれより高くなるとワイヤーの靭性が低下するからである。線引加工後、線引加工時に生じたカール(線ぐせ)を除去するために機械的な方法により直線状に矯正加工し、扱いやすい長さにワイヤーを切断する。その後、500〜600℃の温度で1〜2時間真空または無酸化雰囲気炉で時効処理する。これにより高い機械的強度(特に抗曲力)を有し、靭性に優れているために曲げても破断し難く、耐食性に優れているために錆び難く、表面は光沢があって平滑である、歯の矯正治療における最終段階のわずかな歯の移動を制御して歯を固定するために使用する歯列矯正用ワイヤーを得ることができる。
【0005】
なお、あらかじめ前記方法で時効処理したワイヤーを歯科医に提供し、歯科医が患者の歯並びに合わせてワイヤーを曲げ加工して使用するが、この合金のワイヤーは電気抵抗率が105μΩ−cmと大きいため、時効処理せずに歯科医に提供し、歯科医が曲げ加工をした後にワイヤーに直接電気を流して発熱させる方法で時効処理して使用することもできる。大気中でこの方法で時効処理しても、この合金は酸化し難いので極薄い酸化被膜しか生じないため、表面が荒れてザラザラすることがない。
【0006】
【作用】
前記のような構成により、機械的強度(特に抗曲力)が高く、錆び難く、曲げ加工しても破断し難く、表面状態は光沢があって平滑で、カールがついていないために患者の歯並びに合わせて成形しやすい、歯の矯正治療における最終段階のわずかな歯の移動を制御し
て歯を固定するために使用する歯列矯正用ワイヤーを得ることができる。
【0007】
【実施例】
本発明を詳細に理解してもらうために、以下に実施例について述べる。
組成は重量比でCr20.5%、Mo8.9%、Ni31.3%、Co36.4%、Mn0.4%、Ti0.6%、Al0.1%、Fe0.7%、Nb1.1%、ミッシュメタル0.01%から成る合金を用い、ダイヤモンドダイスを使用して常温で最終加工度80%の線引加工を行い、線径0.40mmの線材にした。
【0008】
図1に線引加工後のカールのついた線材1を示す。その線材を機械的な方法で直線状に矯正加工し、300mmの長さに切断した。直線度は、300mmの長さで直線からの最大離れ幅が1mm以下になるようにした。
図2に線材を直線状に矯正加工する機械的な方法を示す。矢印11、12、13はそれぞれ矯正コマ21、22、23が線材1に加える力の方向を示す。矯正コマ21、22、23は線材1の周りをそれぞれ矢印14、15、16に示す方向に同時に回転する。線材は矢印17の方向に引き出され切断される。
【0009】
図3に直線状に矯正加工して切断した線材3を示す。このようにして仕上げた歯列矯正用ワイヤーと、更にその後550℃で2時間真空熱処理炉を用いて時効処理した歯列矯正用ワイヤーとを用意して、抗曲試験、折り曲げ試験、腐食試験、表面粗さ測定を行った。抗曲試験は25mmの長さに切断したワイヤーを使用して、3点支持曲げにより最大3mmまでワイヤーをたわませて行った。表1に抗曲試験により求めた最大抗曲力を示す。
ここで、最大抗曲力は次の式で表される値である。
【0010】
σmax=9.80665×8WL/πd3
σmax:最大抗曲力(MPa)
W:最大荷重(Kg)
L:支点間距離(12.7mm)
d:ワイヤー径(mm)
本発明ワイヤーは、時効処理することによりハイカーボンステンレス鋼製ワイヤーとほぼ同等の最大抗曲力を有していることがわかる。
【0011】
【表1】
【0012】
次にワイヤーをエッジのコーナーRが0.1mmRのプライヤーを用いて角度90°の折り曲げを繰り返し、何回で破断するかを調べた。破断にいたる回数は、本発明ワイヤーは時効処理前で6回、時効処理後で4回、ハイカーボンステンレス鋼製ワイヤーは3回であった。
【0013】
次に耐食性を調べるために、ワイヤーを液温60℃で10%塩酸に7時間及び10%食塩水に168時間浸漬する腐食試験を行った。その時のワイヤーの単位面積及び単位時間当たりの腐食減量(mg/cm2 ・Hr)または錆の発生状況を表2に示す。本発明ワイヤーはハイカーボンステンレス鋼製ワイヤーに比べ、遙かに耐食性に優れていることがわかる。
【0014】
【表2】
【0015】
次にワイヤーの表面粗さを表3に示す。本発明ワイヤーは、時効処理前も時効処理後もハイカーボンステンレス鋼製ワイヤーに比べ表面粗さを表すRmaxが小さく、平滑であることがわかる。
【0016】
【表3】
【0017】
【発明の効果】
以上説明したように、本発明のワイヤーは、抗曲力が非常に大きく、耐食性に優れているために錆び難く、靭性に優れているために曲げ加工しても破断し難く、表面は光沢があって平滑で、カールがついていないために成形しやすいことから、歯の矯正治療における最終段階のわずかな歯の移動を制御して歯を固定するために使用する歯列矯正用ワイヤーとして最適であるという効果がある。
【0018】
尚、本発明の実施例として円形断面の歯列矯正用ワイヤーの例を記述したが、本発明はこれに限定されるものではなく、歯列矯正治療の目的に適合するように、例えば矩形断面の歯列矯正用ワイヤーを用いても、同様の優れた効果を奏することは上記より明らかである。
【図面の簡単な説明】
【図1】線引加工後のカール(線ぐせ)のついた線材を示す。
【図2】線材を直線状に矯正加工する機械的な方法を示す。
【図3】直線状に矯正加工して切断した線材を示す。
【符号の説明】
1、3 線材
21、22、23 矯正コマ[0001]
[Industrial application fields]
The present invention relates to an orthodontic wire for correcting the alignment of teeth, and is used as a wire for fixing a tooth by controlling a slight movement of the tooth in the final stage of the orthodontic treatment.
[0002]
[Prior art]
In orthodontic treatment, various orthodontic wires are used according to the stage of treatment. In the initial stage of greatly moving the teeth, a Ni-Ti alloy wire having superelasticity is mainly used. An alloy wire having high mechanical strength (particularly anti-curvature) is used in the final stage of orthodontic treatment in which a slight tooth movement is controlled to fix the tooth. Conventionally, as an orthodontic wire used for fixing teeth at the final stage of orthodontic treatment, a high-carbon stainless steel wire that has been heat-treated with a wire diameter of about 0.4 mm has been used.
[0003]
[Problems to be solved by the present invention]
The high carbon stainless steel wire has a high bending strength,
(1) Corrosion resistance is poor and rusts easily.
(2) It tends to break when bent because of poor toughness.
(3) The oxide film generated by the heat treatment causes the surface to become rough, rough and difficult to slip, and hinders control of slight tooth movement.
(4) The wire is curled, and it is difficult to mold the wire to match the patient's teeth arrangement.
It had problems such as.
[0004]
[Means for Solving the Problems]
In order to solve the above-mentioned problems, in the present invention, the material of the wire is a Co—Ni based alloy having high mechanical strength and excellent corrosion resistance and toughness. This Co—Ni based alloy refers to, for example, the alloy of Japanese Patent No. 1374564. The alloy of this patent No. 1374564 is mainly composed of Co, Ni, Cr and Mo, and the composition is Cr + Mo 20 to 40%, Ni 20 to 50%, Co 25 to 45% by weight ratio, Mn, Ti, Al and Fe 0 each. 0.1 to 5%, Nb 0.1 to 3%, Ce, Y, or one or more rare earth elements selected from misch metal, or 0.01 to 1%. Using this alloy, cold drawing is performed at a processing degree of 60 to 90% expressed by a cross-section reduction rate. The reason why the workability is set to 60% or more is that the mechanical strength required for the wire cannot be obtained if the workability is lower than this, and the workability is set to 90% or less. It is because the toughness of a wire will fall when it becomes higher. After the drawing process, straight lines are straightened by a mechanical method in order to remove the curl generated during the drawing process, and the wire is cut to a length that is easy to handle. Thereafter, aging treatment is performed in a vacuum or non-oxidizing atmosphere furnace at a temperature of 500 to 600 ° C. for 1 to 2 hours. Due to this, it has high mechanical strength (particularly anti-bending force), and because it has excellent toughness, it is difficult to break even when bent, and because it has excellent corrosion resistance, it is difficult to rust, the surface is glossy and smooth, It is possible to obtain an orthodontic wire used for fixing a tooth by controlling slight tooth movement in the final stage of the orthodontic treatment.
[0005]
In addition, the wire which has been pre-aged by the above method is provided to the dentist, and the dentist uses the wire by bending the patient's teeth together, but this alloy wire has a large electrical resistivity of 105 μΩ-cm. Therefore, it can be provided to a dentist without being subjected to an aging treatment, and can be used after being subjected to an aging treatment by causing electricity to flow directly through the wire after the dentist performs bending. Even when aging treatment is performed in the air, this alloy is difficult to oxidize, so that only an extremely thin oxide film is formed. Therefore, the surface is not rough and rough.
[0006]
[Action]
With the above configuration, the mechanical strength (particularly the bending force) is high, it is difficult to rust, it is difficult to break even when bent, the surface condition is glossy and smooth, and it is not curled. Accordingly, an orthodontic wire used for fixing a tooth can be obtained by controlling a slight movement of the tooth in the final stage of the orthodontic treatment, which is easy to be molded.
[0007]
【Example】
In order that the present invention may be understood in detail, the following examples are set forth.
The composition is Cr 20.5%, Mo 8.9%, Ni 31.3%, Co 36.4%, Mn 0.4%, Ti 0.6%, Al 0.1%, Fe 0.7%, Nb 1.1% by weight ratio, Using an alloy composed of 0.01% misch metal, a wire rod having a wire diameter of 0.40 mm was drawn at a room temperature using a diamond die at a final working degree of 80%.
[0008]
FIG. 1 shows a curled wire 1 after drawing. The wire was straightened by a mechanical method and cut into a length of 300 mm. The straightness was 300 mm, and the maximum distance from the straight line was 1 mm or less.
FIG. 2 shows a mechanical method for straightening the wire.
[0009]
FIG. 3 shows a
Here, the maximum coercive force is a value represented by the following equation.
[0010]
σmax = 9.80665 × 8 WL / πd 3
σmax: Maximum coercive force (MPa)
W: Maximum load (Kg)
L: Distance between fulcrums (12.7mm)
d: Wire diameter (mm)
It can be seen that the wire of the present invention has a maximum bending force substantially equal to that of the high carbon stainless steel wire by aging treatment.
[0011]
[Table 1]
[0012]
Next, the wire was repeatedly bent at an angle of 90 ° using a pliers having an edge corner R of 0.1 mmR, and the number of breaks was examined. The number of times to break was 6 times before the aging treatment, 4 times after the aging treatment, and 3 times for the high carbon stainless steel wire.
[0013]
Next, in order to investigate the corrosion resistance, a corrosion test was performed in which the wire was immersed in 10% hydrochloric acid for 7 hours and in 168 hours in 10% saline at a liquid temperature of 60 ° C. Table 2 shows the unit area of the wire and the corrosion loss per unit time (mg / cm 2 · Hr) or the occurrence of rust. It turns out that this invention wire is far superior in corrosion resistance compared with the wire made from a high carbon stainless steel.
[0014]
[Table 2]
[0015]
Next, Table 3 shows the surface roughness of the wire. The wire of the present invention has a small Rmax representing the surface roughness as compared to the high carbon stainless steel wire before and after the aging treatment, and is found to be smooth.
[0016]
[Table 3]
[0017]
【The invention's effect】
As described above, the wire of the present invention has a very large bending force and is resistant to rust because of its excellent corrosion resistance, and because of its excellent toughness, it is difficult to break even when bent, and the surface is glossy. Because it is smooth and easy to mold because it is not curled, it is ideal as an orthodontic wire used to fix a tooth by controlling slight tooth movement in the final stage of dental correction treatment. There is an effect that there is.
[0018]
In addition, although the example of the orthodontic wire of circular section was described as an Example of this invention, this invention is not limited to this, For example, in order to suit the objective of orthodontic treatment, rectangular cross section It is clear from the above that even if the orthodontic wire is used, the same excellent effect is obtained.
[Brief description of the drawings]
FIG. 1 shows a wire with curling (drawing) after drawing.
FIG. 2 shows a mechanical method for straightening a wire.
FIG. 3 shows a wire that has been straightened and cut.
[Explanation of symbols]
1, 3
Claims (6)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP15818295A JP3641512B2 (en) | 1994-06-24 | 1995-06-23 | Orthodontic wire and method for manufacturing the same |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP6-143578 | 1994-06-24 | ||
JP14357894 | 1994-06-24 | ||
JP15818295A JP3641512B2 (en) | 1994-06-24 | 1995-06-23 | Orthodontic wire and method for manufacturing the same |
Publications (2)
Publication Number | Publication Date |
---|---|
JPH0867940A JPH0867940A (en) | 1996-03-12 |
JP3641512B2 true JP3641512B2 (en) | 2005-04-20 |
Family
ID=26475269
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP15818295A Expired - Lifetime JP3641512B2 (en) | 1994-06-24 | 1995-06-23 | Orthodontic wire and method for manufacturing the same |
Country Status (1)
Country | Link |
---|---|
JP (1) | JP3641512B2 (en) |
Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JPH11206786A (en) * | 1998-01-23 | 1999-08-03 | Yamaguchi Noboru | Occlusion adjuster |
US6579388B2 (en) | 2001-06-28 | 2003-06-17 | Haynes International, Inc. | Aging treatment for Ni-Cr-Mo alloys |
KR20030003016A (en) * | 2001-06-28 | 2003-01-09 | 하이네스인터내셔널인코포레이티드 | AGING TREATMENT FOR Ni-Cr-Mo ALLOYS |
JP4510542B2 (en) * | 2004-07-30 | 2010-07-28 | セイコーインスツル株式会社 | Cutlery and manufacturing method thereof |
JP2006274443A (en) * | 2005-03-03 | 2006-10-12 | Daido Steel Co Ltd | Nonmagnetc high-hardness alloy |
-
1995
- 1995-06-23 JP JP15818295A patent/JP3641512B2/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
JPH0867940A (en) | 1996-03-12 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US5885381A (en) | Ni-Ti-Pd superelastic alloy material, its manufacturing method, and orthodontic archwire made of this alloy material | |
JP5732468B2 (en) | Nitinol appliance with improved fatigue resistance | |
JP2001020026A (en) | Copper-based alloy having shape memory property and superelasticity, member consisting of the alloy, and their manufacture | |
JP3934372B2 (en) | High strength and low Young's modulus β-type Ti alloy and method for producing the same | |
JP4562830B2 (en) | Manufacturing method of β titanium alloy fine wire | |
JP3641512B2 (en) | Orthodontic wire and method for manufacturing the same | |
JP3842053B2 (en) | High strength low thermal expansion alloy with excellent twisting characteristics and its alloy wire | |
US5692899A (en) | Wire for orthodontic treatment and its manufacturing method | |
JP2009024223A (en) | Dental wire, and method for producing the same | |
JPH0913136A (en) | Spiral spring and its production | |
JP3560907B2 (en) | NiTi-based alloy wire, method for producing the same, and guide wire for catheter using the NiTi-based alloy wire | |
JP2000319758A (en) | Wire rod small in residual scale after mechanical descaling | |
JP5512145B2 (en) | Shape memory alloy | |
JP2009097064A (en) | Ti-BASE ALLOY | |
JP7353300B2 (en) | Medical Pt-Co alloy | |
JP3085099B2 (en) | NiTi-based alloy eyeglass member and method of manufacturing the same | |
JP3379767B2 (en) | Method for producing NiTi-based superelastic material | |
JP2006314525A (en) | Tool to be inserted into tubular organ | |
JP2585168B2 (en) | Method for producing high strength low linear expansion Fe-Ni alloy wire | |
JPH0860277A (en) | Nickel-titanium alloy | |
JP2979420B2 (en) | Orthodontic appliance | |
JP2001187984A (en) | Shape memory alloy tube | |
JPH08283893A (en) | Motor shaft | |
JP2001107206A (en) | beta TITANIUM ALLOY FINE WIRE AND ITS PRODUCTION METHOD | |
JP2004124156A (en) | METHOD FOR MANUFACTURING SUPERELASTIC TiNbSn ALLOY FOR ORGANISM |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
A711 | Notification of change in applicant |
Free format text: JAPANESE INTERMEDIATE CODE: A711 Effective date: 20040106 |
|
A521 | Written amendment |
Free format text: JAPANESE INTERMEDIATE CODE: A821 Effective date: 20040107 |
|
RD01 | Notification of change of attorney |
Free format text: JAPANESE INTERMEDIATE CODE: A7421 Effective date: 20040409 |
|
A521 | Written amendment |
Free format text: JAPANESE INTERMEDIATE CODE: A821 Effective date: 20040409 |
|
A61 | First payment of annual fees (during grant procedure) |
Free format text: JAPANESE INTERMEDIATE CODE: A61 Effective date: 20050124 |
|
R150 | Certificate of patent (=grant) or registration of utility model |
Free format text: JAPANESE INTERMEDIATE CODE: R150 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20080128 Year of fee payment: 3 |
|
S111 | Request for change of ownership or part of ownership |
Free format text: JAPANESE INTERMEDIATE CODE: R313115 |
|
R350 | Written notification of registration of transfer |
Free format text: JAPANESE INTERMEDIATE CODE: R350 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20090128 Year of fee payment: 4 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20100128 Year of fee payment: 5 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20110128 Year of fee payment: 6 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20110128 Year of fee payment: 6 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20120128 Year of fee payment: 7 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20130128 Year of fee payment: 8 |
|
FPAY | Renewal fee payment (prs date is renewal date of database) |
Free format text: PAYMENT UNTIL: 20140128 Year of fee payment: 9 |
|
R250 | Receipt of annual fees |
Free format text: JAPANESE INTERMEDIATE CODE: R250 |
|
R250 | Receipt of annual fees |
Free format text: JAPANESE INTERMEDIATE CODE: R250 |
|
EXPY | Cancellation because of completion of term |