Cyclic deformation behavior of a Ti–26 at.% Nb alloy

Tahara, Masaki; Kim, Hee-Young; Hosoda, Hideki; Miyazaki, S.

doi:10.1016/j.actamat.2009.01.037

Cited by 114 publications

(82 citation statements)

References 36 publications

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“…So from tensile test results, it is concluded that Ti-6Cr-3Sn developed alloy was in metastable state and excellent ductility was due to transformation of metastable phase to stress induced martensite and due to twinning deformation mode during mechanical loading. 18) Vickers hardness test results are given in Fig. 9.…”

Section: Mechanical Propertiesmentioning

confidence: 99%

“…It has been reported that the reverse transformation from 00 (orthorhombic) phase to the phase causes shape recovery to appear. [17][18][19] Ti-Cr is also hopeful alloy system for biomedical applications and there are some reports on mechanical properties of Ti-Cr 20,21) and Ti-Cr-X alloys. [22][23][24][25] Selection of Ti-Cr-Sn alloy system was due to phase stabilizing effect of Cr, low melting points of Cr and Sn as compared to other phase stabilizing elements and solid solution strengthening effect of Cr and Sn (atomic radius: Cr ¼ 0:126 nm, Sn ¼ 0:158 nm, Ti ¼ 0:146 nm).…”

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confidence: 99%

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Comparative Study of Ti-<I>x</I>Cr-3Sn Alloys for Biomedical Applications

et al. 2011

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In order to replace toxic nickel element from NiTi biomaterials, Ti-Cr and Ti-Cr-X alloys are also new nickel free titanium based alloys for biomedical applications. In this study, comparative study of Ti-xCr-3Sn (x ¼ 4, 5, 6, 7, 8 and 9 mol%) alloys was carried out. Ti-4Cr-3Sn and Ti5Cr-3Sn alloys were composed of 0 martensitic phase (hcp) and other alloys with 6, 7, 8 and 9 mol% Cr were single phase at room temperature. Among the developed alloys, Ti-6Cr-3Sn alloy showed maximum fracture strain, maximum shape memory effect, maximum pseudoelastic response and minimum hardness and minimum yield stress due to transformation of metastable phase to stress induced martensite during mechanical loading. Vickers hardness and UTS has increased and fracture strain has decreased with greater than 6 mol% addition of chromium in Ti-xCr-3Sn alloys due to solid solution strengthening, phase stabilization and slip as dominant deformation mechanism. It is concluded that among the developed Ti-xCr-3Sn alloys, Ti-6Cr-3Sn alloy is hopeful new alloy for biomedical applications.

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Section: Mechanical Propertiesmentioning

confidence: 99%

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confidence: 99%

Comparative Study of Ti-<I>x</I>Cr-3Sn Alloys for Biomedical Applications

et al. 2011

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“…Nevertheless, further microstructural analyzes, such as transmission electron microscopy have to be done to confirm that explanation. It is also noticed from Figure 4 that no peak related to the martensitic phase was detected by the XRD analyzes, which suggests that either the number of cycles or the strain amplitude used in the training were not enough to stabilize martensite [14,29,30]. …”

Section: * Technical Contribution To the 71º Congresso Anual Da Abm -mentioning

confidence: 90%

Influence of Strain Rate on the Functional Behavior of a Niti Alloy Under Pseudoelastic Training

Rodrigues¹,

Soares²,

Buono³

et al. 2017

Anais Do Congresso Anual Da ABM

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The present study deals with the effects of strain rate on the functional behavior of NiTi thin wires. The samples, in the austenitic condition at room temperature, were mechanically cycled 20 times by loading up to 6% strain followed by complete unloading, at 25°C. Four different quasi-static strain rates were assessed: 1x10 . The functional properties are described by means of critical stress to induce martensite, stress at maximum strain, energy dissipated per cycle and residual strain. The sensitivity of repeated cyclic deformation to strain rate is also analyzed in terms of phase stability. The results show that the fluctuation in the loading plateau, due to non-homogeneous transformation, increases with increasing strain rate. During cycling, it is observed that higher strain rates result in lower critical stress to induce martensite after the 5th cycle. However, the stress at maximum strain is higher at high strain rates, regardless the number of cycles. The accumulation of residual strain also increases with the strain rate due to the higher applied stress. During unloading, both the elastic deformation of stress-induced martensite and the reverse transformation seem to overlap at high strain rates. The dissipated energy behavior changes between the 1st and 20th cycle. No martensite is stabilized after training, but the intensity of the X-ray diffraction peaks of austenite increases with strain rate, as a result of stress relaxation.

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“…Al-Zain et al and Tahara et al performed in situ X-ray diffraction studies on Ti-26Nb and Ti-13Nb-4Mo alloys (at%) and detected the SIM α″ phase transformation [144,145]. The α″ phase is shown to be formed from 0.2% to 2.5% of strain and to be partially reversible after unloading from 2.5% strain [144][145][146]. These experiments were performed using a deformation of 2.5% which was followed by unloading.…”

Section: Identification Of α″ Phasementioning

confidence: 99%

“…Some previous work tried to stabilise SIM α″ by cyclic deformation and severe deformation [38,146,190]. It has been accepted that the stabilisation is due to the interruption of the reverse martensitic transformation by dislocations introduced during prior plastic deformation.…”

Section: Twinning Identificationmentioning

confidence: 99%

Mechanical and microstructural characterisation in the processing of biomedical metallic fine tubes

Yao-wu¹

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Fine tube stents are used for maintaining localised flow in stenotic blood vessels. Elasticity and plasticity for expansion, rigidity for resisting bending under force and strength to prevent unexpected failure, are required properties of the tubes from which these stents are formed. Biomedical metastable β titanium alloys have been developed as implant materials for a large number of biomedical applications due to a combination of favourable characteristics, e.g. good biocompatibility, excellent toughness and corrosion resistance. A metastable β alloy, Ti-25Nb-3Mo-3Zr-2Sn, has been developed without toxic alloying elements, which is a promising candidate material for stent applications. Metallic materials used for stents are commonly not biodegradable and implanted in the vessel permanently, which may provoke in-stent restenosis and stent thrombosis. In order to remove the implanted materials after service, biodegradable materials, absorbed by the body slowly, are also a field of research interest. Magnesium alloys have been used in studies for biomedical stent applications as a new biodegradable material. Magnesium stents can reopen the blocked blood vessels temporarily before degrading in physiological environments. In addition to the biodegradable characteristics, their mechanical properties are reasonable. The Mg-3Al-1Zn (AZ31) alloy is the subject of some research on the processing of biomedical magnesium alloys as it is a commonly available commercial alloy. Consequently, the Ti-25Nb-3Mo-3Zr-2Sn alloy and the AZ31 magnesium alloy have been used in this thesis to investigate the evolution of mechanical properties and microstructure in the processing of fine tubes.The deformation mechanisms during cold deformation of metastable β titanium alloys are mainly associated with martensitic phase transformations and mechanical twinning. It has been reported that stress-induced phase transformations and {112}〈111〉, {332}〈113〉 twinning modes may be activated under different stress states in metastable β titanium alloys. They can exhibit varying elasticity, Young's modulus and strain hardening behaviour. Because the martensitic start temperature is below room temperature for most metastable β titanium alloys, the α″ martensitic transformation can easily occur under a small amount of external stress. Mechanical twins were reported to hinder slip and dislocation motion thereby increasing the strain hardening rate. The development of β and α″ texture during processing is another critical influence on the mechanical properties of fine tubes. Therefore, studies on the martensitic transformation, mechanical twins and texture evolution is of significance in order to understand the processing of β titanium fine tubes.ii Magnesium alloys deform through the formation of a large amount of mechanical twins due to the relatively low critical stress to activate twinning in comparison with 〈 + 〉 slip. There are typically two primary mechanical twinning modes for magnesium alloys, {101 ̅ 2} extension twins and {101 ̅ 1} cont...

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Cyclic deformation behavior of a Ti–26 at.% Nb alloy

Cited by 114 publications

References 36 publications

Comparative Study of Ti-<I>x</I>Cr-3Sn Alloys for Biomedical Applications

Comparative Study of Ti-<I>x</I>Cr-3Sn Alloys for Biomedical Applications

Influence of Strain Rate on the Functional Behavior of a Niti Alloy Under Pseudoelastic Training

Mechanical and microstructural characterisation in the processing of biomedical metallic fine tubes

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