Electrochemical and surface characterization of a nickel–titanium alloy

Wever, Dirk Jan; Veldhuizen, Albert G.; Vries, J. de; Busscher, Hj; Uges, Dra; Horn, J.R. van

doi:10.1016/s0142-9612(97)00210-x

Cited by 401 publications

(206 citation statements)

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“…Previous immersion testing demonstrated that polished Nitinol exhibits similar Ni release behavior to stainless steels and cobalt-based alloys [9,10]. Longer immersion studies (up to 6 months) found that surface treatments such as polishing and/or passivation of Nitinol wires can reduce Ni release compared to untreated controls [11][12][13][14]. Wire immersion tests have shown that thicker oxides, surface Ni particles, and Ni-rich phases contribute to increased Ni dissolution [15,16].…”

Section: Introductionmentioning

confidence: 99%

Effects of Oxide Layer Composition and Radial Compression on Nickel Release in Nitinol Stents

Sullivan

Dreher

Zheng

et al. 2015

Shap. Mem. Superelasticity

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There is a public health need to understand the effects of surface layer thickness and composition on corrosion in nickel-containing medical devices. To address this knowledge gap, five groups of Nitinol stents were manufactured by various processing methods that altered the titanium oxide layer. The following surfaces were created: [3500 nm thick mixed thermal oxide (OT), *420 nm thick mixed thermal oxide (SP), *130 nm thick mixed thermal oxide (AF), *4 nm thick native oxide (MP), and an *4 nm thick passivated oxide (EP). Radially compressed and not compressed devices were evaluated for nickel (Ni) ion release in a 60-day immersion test. The results indicated that OT stents released the most Ni, followed by stents in the SP and AF groups. For OT and SP stents, which exhibited the thickest oxide layers, radial compression significantly increased Ni release when compared to non-compressed stents. This result was not observed in AF, MP, SP stents indicating that the increased Ni release may be explained by cracking of the thicker oxide layers during crimping. Strong correlations were observed between oxide layer thickness and cumulative Ni release. These findings elucidate the importance of oxide layer thickness and composition on uniform corrosion of laser-cut Nitinol stents.

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Section: Introductionmentioning

confidence: 99%

Effects of Oxide Layer Composition and Radial Compression on Nickel Release in Nitinol Stents

Sullivan

Dreher

Zheng

et al. 2015

Shap. Mem. Superelasticity

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“…The overall inflammatory response of the nickel-titanium alloy was comparable to both other alloys. The good biocompatibility and the associated good anti-corrosive properties of the shape-memory metal may be ascribed to the strong bonding between the nickel and titanium atoms, and the presence of a mainly passive, TiO 2 -based, surface layer [25,38]. This protective, chemically stable, oxidized passivation layer is also thought to be responsible for the good anti-corrosive properties and tissue compatibility of the titanium alloy, Ti6Al4 V [15,20].…”

Section: Discussionmentioning

confidence: 99%

“…Moreover, studies have revealed that titanium-based alloys naturally form a calcium-phosphate layer on their passive oxide film after exposure to a bioenvironment. It is suggested that the formation and growth of this layer is governed by the existence of titanium oxide, and may serve as a further barrier against ion diffusion [14,38]. However, biological safety is not only determined by the corrosive properties and the potential toxicity of the used metal, but also by the construction design of the device.…”

Section: Discussionmentioning

confidence: 99%

“…The determination of the serum nickel concentration was achieved using atomic absorption spectrometry [38]. After being positioned, the animals were shaved, disinfected and covered with a sterile cloth.…”

Section: Surgical Proceduresmentioning

confidence: 99%

“…The transition temperature of the rod, i.e., the temperature at which low-temperature phase martensite changes to the high-temperature phase austenite, was 25°C. For the composition and surface treatment of the used shape-memory alloy, the reader is referred to the articles on corrosion and biocompatibility [37,38]. The rod had been stored in sterile conditions at -18°C.…”

Section: Surgical Proceduresmentioning

confidence: 99%

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Scoliosis correction with shape-memory metal: results of an experimental study

et al. 2001

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IntroductionOperations for scoliosis are designed to correct the deformity and to prevent its progression by achieving a solid fusion. In 1962, Harrington introduced the use of spinal instrumentation for the surgical treatment of scoliosis [16]. In the 1980s, the development of spinal instrumentation expanded considerably. New anterior and posterior systems were introduced [2,6,10,12,18,32]. With these advanced segmental systems, better corrections are possible in the coronal and the sagittal plain in comparison with Harrington instrumentation. However, the literature is contradictory on the effect on axial rotation and rib cage deformity. In most literature it is suggested that axial plane correction is limited [13,19,21,33].Abstract The biocompatibility and functionality of a new scoliosis correction device, based on the properties of the shape-memory metal nickel-titanium alloy, were studied. With this device, the shape recovery forces of a shape-memory metal rod are used to achieve a gradual threedimensional scoliosis correction. In the experimental study the action of the new device was inverted: the device was used to induce a scoliotic curve instead of correcting one. Surgical procedures were performed in six pigs. An originally curved squared rod, in the cold condition, was straightened and fixed to the spine with pedicle screws. Peroperatively, the memory effect of the rod was activated by heating the rod to 50°C by a low-voltage, high-frequency current. After 3 and after 6 months the animals were sacrificed. The first radiographs, obtained immediately after surgery, showed in all animals an induced curve of about 40°Cobb angle -the original curve of the rod. This curve remained constant during the followup. The postoperative serum nickel measurements were around the detection limit, and were not significantly higher compared to the preoperative nickel concentration. Macroscopic inspection after 3 and 6 months showed that the device was almost overgrown with newly formed bone. Corrosion and fretting processes were not observed. Histologic examination of the sections of the surrounding tissues and sections of the lung, liver, spleen and kidney showed no evidence of a foreign body response. In view of the initiation of the scoliotic deformation, it is expected that the shape-memory metal based scoliosis correction device also has the capacity to correct a scoliotic curve. Moreover, it is expected that the new device will show good biocompatibility in clinical application. Extensive fatigue testing of the whole system should be performed before clinical trials are initiated.

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Bone healing and mineralization, implant corrosion, and trace metals after nickel-titanium shape memory metal intramedullary fixation

Ryhänen

Kallioinen

Serlo

et al. 1999

J. Biomed. Mater. Res.

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Its shape memory effect, superelasticity, and good wear and damping properties make the NiTi shape memory alloy a material with fascinating potential for orthopedic surgery. It provides a possibility for making self-locking, self-expanding, and self-compressing implants. Problems, however, may arise because of its high nickel content. The purpose of this work was to determine the corrosion of NiTi in vivo and to evaluate the possible deleterious effects of NiTi on osteotomy healing, bone mineralization, and the remodeling response. Femoral osteotomies of 40 rats were fixed with either NiTi or stainless steel (StSt) intramedullary nails. The rats were killed at 2, 4, 8, 12, 26, and 60 weeks. Bone healing was examined with radiographs, peripheral quantitative computed tomography, (pQCT) and histologically. The corrosion of the retrieved implants was analyzed by electron microscopy (FESEM). Trace metals from several organs were determined by graphite furnace atomic absorption spectrometry (GF-AAS) or by inductively coupled plasma-atomic emission spectrometry (ICP-AES). There were more healed bone unions in the NiTi than in the StSt group at early (4 and 8 weeks) time points. Callus size was equal between the groups. The total and cortical bone mineral densities did not differ between the NiTi and StSt groups. Mineral density in both groups was lower in the osteotomy area than in the other areas along the nail. Density in the nail area was lower than in the proximal part of the operated femur or the contralateral femur. Bone contact to NiTi was close. A peri-implant lamellar bone sheet formed in the metaphyseal area after 8 weeks, indicating good tissue tolerance. The FESEM assessment showed surface corrosion changes to be more evident in the StSt implants. There were no statistically significant differences in nickel concentration between the NiTi and StSt groups in any of the organs. NiTi appears to be an appropriate material for further intramedullary use because it has good biocompatibility in bone tissue.

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Electrochemical and surface characterization of a nickel–titanium alloy

Cited by 401 publications

References 0 publications

Effects of Oxide Layer Composition and Radial Compression on Nickel Release in Nitinol Stents

Effects of Oxide Layer Composition and Radial Compression on Nickel Release in Nitinol Stents

Scoliosis correction with shape-memory metal: results of an experimental study

Bone healing and mineralization, implant corrosion, and trace metals after nickel-titanium shape memory metal intramedullary fixation

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