CN103938003A - Preparation method of Ni-Ti-Cu alloy dental arch wire - Google Patents
Preparation method of Ni-Ti-Cu alloy dental arch wire Download PDFInfo
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- CN103938003A CN103938003A CN201410179460.5A CN201410179460A CN103938003A CN 103938003 A CN103938003 A CN 103938003A CN 201410179460 A CN201410179460 A CN 201410179460A CN 103938003 A CN103938003 A CN 103938003A
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Abstract
The invention discloses a preparation method of a Ni-Ti-Cu alloy dental arch wire. The material of the dental arch wire is a Ni-Ti-Cu alloy comprising the following raw materials in percentage by weight: 50.14% of Ni, 43.93% of Ti and 5.93% of Cu. The preparation method comprises the following steps: preparing a Ni-Ti-Cu cast ingot through vacuum consumable arc melting, forging, rolling, performing wire drawing, and sizing to prepare the Ni-Ti-Cu dental arch wire. The invention has the following advantages: the stress required for reorientation of a martensitic phase variant is low, which means that the reorientation of the martensitic variant is easy to perform, and the deformational stress or yield strength under martensitic conditions is reduced; the addition of Cu can increase the yield strength of the parent phase B2, thereby increasing the yield strength difference between the parent phase and the martensitic phase, and enhancing the phase change circulation behavior; the stress lag of the superelasticity of the Ni-Ti-Cu alloy is relatively small, thus ensuring that the Ni-Ti-Cu alloy is a favorable superelastic material; and the Cu content in the Ni-Ti-Cu is 5-10 at.% to replace Ni, thereby greatly lowering the raw material cost further.
Description
Technical field
The present invention relates to a kind of preparation method of dental arch filament, relate in particular to a kind of preparation method of Ni-Ti-Cu alloy dental arch filament.
Background technology
Countries in the world are most popular in mouth cavity orthodontic is clinical is fixed appliance, and rescues the main functional parts that arch wire is rectifier.In deformation process, produce by rescuing arch wire the movement that continues and there is a certain size elastic force control tooth rescuing in process just, reach the object of rescuing.Visible, rescuing arch wire material has epochmaking impact to mouth cavity orthodontic process and effect.Therefore, develop and develop and new meet the clinical required arch wire material of correction and become correction clinicist and Materials science worker's common task.The main orthopedic wire using has Stainless Steel Wire and NiTi shape-memory alloy wire in the market.Because NiTi silk has shape memory effect and super-elasticity, in therapeutic process, can provide gentleness and the lasting power of rescuing, become the first-selected product of correction dental arch filament.But the transformation temperature of NiTi alloy is very responsive to Ni content, Ni content 0.1at%, martensite reverses and becomes final temperature A
fto change 10 ~ 20 DEG C, this is extremely unfavorable for the product stability of NiTi dental arch filament.Adding of element Cu can suppress the susceptibility of NiTi alloy phase change temperature to composition, and the hysteresis of phase transformation is obviously narrowed.With NiTi alloy phase ratio, the required stress of NiTiCu alloy martensite phase variant reorientation is lower, means that the reorientation of martensite variants is easily carried out, and reduces deforming stress or yield strength under martensitic state; The interpolation of Cu can improve the yield strength of parent phase B2, thereby strengthens the yield strength difference of parent phase and martensitic phase, strengthens its phase transformation circulation behavior; The hyperelastic stress of NiTiCu alloy lags behind smaller, is a kind of good elastic material; Cu content in NiTiCu is 5 ~ 10at.% to replace Ni, also can significantly reduce material cost.Therefore, adopt vacuum consumable arc-melting to prepare NiTiCu ingot casting, then prepare NiTiCu dental arch filament through forging, rolling, wire drawing and sizing, to replace existing NiTi alloy.
Summary of the invention
The object of the present invention is to provide a kind of preparation method of Ni-Ti-Cu alloy dental arch filament, to replace existing NiTi dental arch filament.
To achieve these goals, technical scheme of the present invention is: a kind of preparation method of Ni-Ti-Cu alloy dental arch filament, it is characterized in that, weight alloy percentage composition is: Ni 50.14%, Ti 43.93%, Cu 5.93%, foreign matter content is carbon≤0.05%, hydrogen≤0.005%, oxygen≤0.05%, nitrogen≤0.05%.
A preparation method for Ni-Ti-Cu alloy dental arch filament, its step comprises vacuum consumable arc-melting, forging, rolling, drawing and sizing.
In described vacuum consumable arc-melting, starting material used are titanium sponge, electrolytic nickel and electrolytic copper powder, compressed together, form cylindric electrode, and melting voltage is 20 ~ 50V, and electric current is in 1000A～300A scope, and vacuum tightness is not less than 10
-2pa, obtains ingot casting blank.
In described forging, Heating temperature, between 950 ~ 1100 DEG C, is incubated 30 ~ 180 minutes.
In described rolling, Heating temperature, between 800 ~ 900 DEG C, is incubated 30 ~ 60 minutes.
In described drawing, comprise hot drawing and cold-drawn, hot drawing Heating temperature is between 700 ~ 800 DEG C, and draw speed is 0.5 ~ 1.2m/s; Cold-drawn single pass heavy deformation is 10% ~ 15%, in the time that accumulative total deflection is 30% ~ 40%, carries out 700 ~ 800 DEG C of stress relief annealings.
In described sizing, setting temperature, between 500 ~ 550 DEG C, is incubated 5 ~ 10 minutes, water quenching.
NiTiCu shape memory alloy dental arch of the present invention utilizes vacuum consumable arc-melting.Utilize titanium sponge, electrolytic nickel, copper powder to prepare burden by a certain percentage, alloy material process is pressed into electrode, then through vacuum consumable arc-melting secondary or three one-tenth ingot castings, then through hot and cold dental arch filaments that is processed to form such as forging, rolling, drawing and sizings.
The present invention compared with prior art tool has the following advantages: the required stress of martensitic phase variant reorientation is lower, means that the reorientation of martensite variants is easily carried out, and reduces deforming stress or yield strength under martensitic state; The interpolation of Cu can improve the yield strength of parent phase B2, thereby strengthens the yield strength difference of parent phase and martensitic phase, strengthens its phase transformation circulation behavior; The hyperelastic stress of NiTiCu alloy lags behind smaller, is a kind of good elastic material; Cu content in NiTiCu is 5 ~ 10at.% to replace Ni, also can significantly reduce material cost.
Embodiment
Below embodiments of the invention are described in further detail, but the present embodiment is not limited to the present invention, every employing analog structure of the present invention and similar variation thereof, all should list protection scope of the present invention in.
embodiment 1
Taking titanium sponge, electrolytic nickel, electrolytic copper powder as starting material, gross weight is 5 kilograms, and the designing quality of each component is respectively: titanium: 2.20 kilograms, and nickel: 2.51 kilograms, copper: 0.29 kilogram.In starting material, carbon is 0.05%, hydrogen is 0.005%, oxygen is 0.05%, nitrogen is 0.05%.Starting material are mixed to the electrode that is pressed into 5 kilograms, be smelted into cylinder ingot casting through secondary vacuum consumable electroarc furnace, melting useful vacuum degree is not less than 10
-2pa, electric current is in 1000A～300A scope, and voltage is 30 ~ 40V.Ingot casting is incubated 180 minutes hammer coggings at 1100 DEG C.Then progressively forge the pole that formation diameter is 28mm at 900 DEG C.Then carry out 800 DEG C of rollings, the crin that formation diameter is 4mm.At 700 DEG C, carry out afterwards drawing, drawing speed is 0.7m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 0.8mm after serial drawing.Subsequently, scale removal, carries out cold-drawn, and drawing speed is 0.5m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 0.53mm after serial drawing.Carry out again, after scale removal, at 500 DEG C, being incubated 10 minutes and carrying out heat treatment, subsequently water quenching.Remove after oxidation, obtain diameter and be the circular dental arch filament of 0.02 inch.
embodiment 2
Taking titanium sponge, electrolytic nickel, electrolytic copper powder as starting material, gross weight is 5 kilograms, and the designing quality of each component is respectively: titanium: 2.20 kilograms, and nickel: 2.51 kilograms, copper: 0.29 kilogram.In starting material, carbon is 0.05%, hydrogen is 0.005%, oxygen is 0.05%, nitrogen is 0.05%.Starting material are mixed to the electrode that is pressed into 5 kilograms, be smelted into cylinder ingot casting through secondary vacuum consumable electroarc furnace, melting useful vacuum degree is not less than 10
-2pa, electric current is in 1000A～300A scope, and voltage is 30 ~ 40V.Ingot casting is incubated 180 minutes hammer coggings at 1100 DEG C.Then progressively forge the pole that formation diameter is 28mm at 900 DEG C.Then carry out 800 DEG C of rollings, the crin that formation diameter is 4mm.At 700 DEG C, carry out afterwards drawing, drawing speed is 0.7m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 0.5mm after serial drawing.Subsequently, scale removal, carries out cold-drawn, and drawing speed is 0.5m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 0.32mm after serial drawing.Carry out again, after scale removal, at 500 DEG C, being incubated 10 minutes and carrying out heat treatment, subsequently water quenching.Remove after oxidation, obtain diameter and be the circular dental arch filament of 0.012 inch.
embodiment 3
Taking titanium sponge, electrolytic nickel, electrolytic copper powder as starting material, gross weight is 5 kilograms, and the designing quality of each component is respectively: titanium: 2.20 kilograms, and nickel: 2.51 kilograms, copper: 0.29 kilogram.In starting material, carbon is 0.05%, hydrogen is 0.005%, oxygen is 0.05%, nitrogen is 0.05%.Starting material are mixed to the electrode that is pressed into 5 kilograms, be smelted into cylinder ingot casting through secondary vacuum consumable electroarc furnace, melting useful vacuum degree is not less than 10
-2pa, electric current is in 1000A～300A scope, and voltage is 30 ~ 40V.Ingot casting is incubated 180 minutes hammer coggings at 1100 DEG C.Then progressively forge the pole that formation diameter is 28mm at 900 DEG C.Then carry out 800 DEG C of rollings, the crin that formation diameter is 4mm.At 700 DEG C, carry out afterwards drawing, drawing speed is 0.7m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 0.7mm after serial drawing.Subsequently, scale removal, carries out square dies hot drawing, and drawing speed is 0.5m/s, is drawn to 0.56 mm × 0.56mm.Scale removal, is cold drawing to 0.43 mm × 0.43 mm.Carry out again, after scale removal, at 500 DEG C, being incubated 10 minutes and carrying out heat treatment, subsequently water quenching.Remove after oxidation, obtain the square dental arch filament of 0.016 inch × 0.016 inch.
embodiment 4
Taking titanium sponge, electrolytic nickel, electrolytic copper powder as starting material, gross weight is 5 kilograms, and the designing quality of each component is respectively: titanium: 2.20 kilograms, and nickel: 2.51 kilograms, copper: 0.29 kilogram.In starting material, carbon is 0.05%, hydrogen is 0.005%, oxygen is 0.05%, nitrogen is 0.05%.Starting material are mixed to the electrode that is pressed into 5 kilograms, be smelted into cylinder ingot casting through secondary vacuum consumable electroarc furnace, melting useful vacuum degree is not less than 10
-2pa, electric current is in 1000A～300A scope, and voltage is 30 ~ 40V.Ingot casting is incubated 180 minutes hammer coggings at 1100 DEG C.Then progressively forge the pole that formation diameter is 28mm at 900 DEG C.Then carry out 800 DEG C of rollings, the crin that formation diameter is 4mm.At 700 DEG C, carry out afterwards drawing, drawing speed is 0.7m/s, and single pass heavy deformation is 10%, obtains the filament that diameter is 1.0mm after serial drawing.Subsequently, scale removal, carries out square dies hot drawing, and drawing speed is 0.5m/s, is drawn to 0.8mm × 0.7mm.Scale removal, is cold drawing to 0.64mm × 0.54mm.Carry out again, after scale removal, at 500 DEG C, being incubated 10 minutes and carrying out heat treatment, subsequently water quenching.Remove after oxidation, obtain the square dental arch filament of 0.025 inch × 0.021 inch.
Claims (6)
1. the preparation method of a Ni-Ti-Cu alloy dental arch filament, it is characterized in that weight alloy percentage composition is: Ni 50.14%, Ti 43.93%, Cu 5.93%, foreign matter content is carbon≤0.05%, hydrogen≤0.005%, oxygen≤0.05%, nitrogen≤0.05%, its step comprises vacuum consumable arc-melting, forge, rolling, drawing and sizing, utilize vacuum consumable arc-melting, titanium sponge, electrolytic nickel, copper powder is prepared burden by a certain percentage, alloy material is through being pressed into electrode, again through vacuum consumable arc-melting secondary or three one-tenth ingot castings, then through forging, rolling, drawing and sizing etc. are cold, hot-work forms dental arch filament.
2. the preparation method of a kind of Ni-Ti-Cu alloy dental arch filament according to claim 1, it is characterized in that, described vacuum consumable arc-melting, starting material used are titanium sponge, electrolytic nickel and electrolytic copper powder, compressed together, form cylindric electrode, melting voltage is 20 ~ 50V, electric current is in 1000A～300A scope, and vacuum tightness is not less than 10
-2pa, obtains ingot casting blank.
3. the preparation method of a kind of Ni-Ti-Cu alloy dental arch filament according to claim 1, is characterized in that, described forging, and Heating temperature, between 950 ~ 1100 DEG C, is incubated 30 ~ 180 minutes.
4. the preparation method of a kind of Ni-Ti-Cu alloy dental arch filament according to claim 1, is characterized in that, described rolling, and Heating temperature, between 800 ~ 900 DEG C, is incubated 30 ~ 60 minutes.
5. the preparation method of a kind of Ni-Ti-Cu alloy dental arch filament according to claim 1, is characterized in that, described drawing comprises hot drawing and cold-drawn, and hot drawing Heating temperature is between 700 ~ 800 DEG C, and draw speed is 0.5 ~ 1.2m/s; Cold-drawn single pass heavy deformation is 10% ~ 15%, in the time that accumulative total deflection is 30% ~ 40%, carries out 700 ~ 800 DEG C of stress relief annealings.
6. the preparation method of a kind of Ni-Ti-Cu alloy dental arch filament according to claim 1, is characterized in that, described sizing, and setting temperature, between 500 ~ 550 DEG C, is incubated 5 ~ 10 minutes, water quenching.
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104164578A (en) * | 2014-08-30 | 2014-11-26 | 海安南京大学高新技术研究院 | Low-modulus high-corrosion-resistance ternary Ni-Ti-Cu alloy and preparation method thereof |
| CN105268973A (en) * | 2015-10-29 | 2016-01-27 | 沈阳海纳鑫科技有限公司 | Additive manufacturing method for functional material part based on TiNi memory alloy wire |
| CN107142396A (en) * | 2016-03-01 | 2017-09-08 | 广州市帕菲克义齿科技有限公司 | The preparation method of Ni-Ti-Cu alloy dental arch filaments |
| CN109666813A (en) * | 2019-03-05 | 2019-04-23 | 西安斯塔克材料科技有限公司 | A kind of preparation method of high purity titanium ambrose alloy marmem ingot casting |
| CN113559333A (en) * | 2021-06-07 | 2021-10-29 | 中国科学院金属研究所 | Medical nickel-titanium alloy with high anticoagulation function without surface treatment |
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| US6280539B1 (en) * | 1990-12-18 | 2001-08-28 | Advance Cardiovascular Systems, Inc. | Superelastic guiding member |
| CN103243240A (en) * | 2013-04-27 | 2013-08-14 | 西安赛特金属材料开发有限公司 | Preparation method of high-plasticity TiNi51 alloy wire material |
| CN103658205A (en) * | 2012-09-04 | 2014-03-26 | 西安思维金属材料有限公司 | Method for processing titanium-nickel base shape memory alloy profiled bar |
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| US6280539B1 (en) * | 1990-12-18 | 2001-08-28 | Advance Cardiovascular Systems, Inc. | Superelastic guiding member |
| CN103658205A (en) * | 2012-09-04 | 2014-03-26 | 西安思维金属材料有限公司 | Method for processing titanium-nickel base shape memory alloy profiled bar |
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Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104164578A (en) * | 2014-08-30 | 2014-11-26 | 海安南京大学高新技术研究院 | Low-modulus high-corrosion-resistance ternary Ni-Ti-Cu alloy and preparation method thereof |
| CN105268973A (en) * | 2015-10-29 | 2016-01-27 | 沈阳海纳鑫科技有限公司 | Additive manufacturing method for functional material part based on TiNi memory alloy wire |
| CN107142396A (en) * | 2016-03-01 | 2017-09-08 | 广州市帕菲克义齿科技有限公司 | The preparation method of Ni-Ti-Cu alloy dental arch filaments |
| CN109666813A (en) * | 2019-03-05 | 2019-04-23 | 西安斯塔克材料科技有限公司 | A kind of preparation method of high purity titanium ambrose alloy marmem ingot casting |
| CN113559333A (en) * | 2021-06-07 | 2021-10-29 | 中国科学院金属研究所 | Medical nickel-titanium alloy with high anticoagulation function without surface treatment |
| CN113559333B (en) * | 2021-06-07 | 2022-11-08 | 中国科学院金属研究所 | Medical nickel-titanium alloy with high anticoagulation function without surface treatment |
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Application publication date: 20140723 |