Thermal decomposition of bioactive sodium titanate surfaces

Ravelingien, Matthieu; Mullens, Steven; Luyten, Jan; Meynen, Vera; Vinck, Evi; Vervaet, Chris; Remon, Jean Paul

doi:10.1016/j.apsusc.2009.07.091

Cited by 25 publications

(7 citation statements)

References 13 publications

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“…Vacuum heating of NaOH‐treated Ti metal reportedly produced low‐valence suboxides and lost apatite‐forming ability, 14 which is a similar tendency to that of the present results. Although the surface of NaOH‐treated TiO is almost covered by the apatite particles, the intensity of TF‐XRD patterns of the apatite was smaller than the other NaOH‐treated titanias (Figures 6 and 7).…”

Section: Discussionsupporting

confidence: 89%

“…This assumption is also supported by the fact that when TiO and Ti 2 O 3 were initially treated with NaOH solution, the surface titania became tetravalent and the apatiteforming ability was significantly enhanced (Figures 6 and 7). It is considered that TiO and Ti 2 O 3 were oxidized as follows by NaOH treatment: Vacuum heating of NaOH-treated Ti metal reportedly produced low-valence suboxides and lost apatite-forming ability, 14 which is a similar tendency to that of the present results. Although the surface of NaOH-treated TiO is almost covered by the apatite particles, the intensity of TF-XRD patterns of the apatite was smaller than the other NaOH-treated titanias (Figures 6 and 7).…”

Section: Discussionsupporting

confidence: 84%

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Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Miyazaki

Akaike

2021

J. Am. Ceram. Soc.

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Titania-based materials are attractive for hard tissue repair due to their bone-bonding ability induced by apatite formation in the body environment. Various surface treatments have therefore been developed to produce a hydrated titania layer on Ti and its alloys. Titania takes various valences, such as TiO (Ti 2+ ) and Ti 2 O 3 (Ti 3+ ), as well as typical TiO 2 (Ti 4+ ); however, there is no comprehensive study of structural effects on the apatite-forming ability of these titanias. In this study, we investigated apatite formation on titania powders with various valences in simulated body fluid. Anataseand rutile-type TiO 2 formed apatite in simulated body fluid within 7 days, but TiO and Ti 2 O 3 did not. In contrast, when the titania powders were treated with NaOH solution, the surface converted to tetravalent titania and all samples formed apatite.It is proposed that the surface electrical states of TiO and Ti 2 O 3 are strongly affected by their bulk conductivity and that these behaved like pure Ti metal, which has poor apatite-forming ability. Apatite formation was favorable when the titania had a high absolute value and exhibited high fluctuations of zeta potential during initial stages in simulated body fluid, owing to adsorption of large amounts of Ca 2+ and HPO 4 2− . K E Y W O R D Sapatite, bioactivity, calcium phosphate, titanium oxide | MATERIALS AND METHODS | SpecimensDivalent TiO, trivalent Ti 2 O 3 (Kojundo Chemical Lab. Co., Ltd., Japan), tetravalent anatase-type TiO 2 (MC-50, average primary particle size: 24 nm; Ishihara Sangyo Kaisha Ltd., Japan, and FUJIFILM Wako Pure Chemical Co., Japan), and rutile-type TiO 2 (FUJIFILM Wako Pure Chemical Co.) were used. The particle sizes of TiO and Ti 2 O 3 were relatively large (around 1-5 mm), so these reagents were ground in a mortar for 7 minutes prior to use.

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Section: Discussionsupporting

confidence: 89%

Section: Discussionsupporting

confidence: 84%

Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Miyazaki

Akaike

2021

J. Am. Ceram. Soc.

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“…The specimens were then heated to 600°C at a rate of 5°C min −1 , kept at 600°C for 1 hour and finally allowed to cool in the furnace. 11,22 For H 2 O 2 treatment, the specimens were immersed in 15 ml/specimen solution containing 8.8 M H 2 O 2 and 0.1 M HCl at 80°C for 30 minutes; then, they were heated to 500°C at a rate of 5°C min −1 , kept at 500°C for 1 hour and finally allowed to cool in the furnace. 23 For heat treatment, the specimens were heated up to 500°C in the air at a rate of 5°C min −1 , kept at 500°C for 1 hour and then allowed to cool in the furnace.…”

Section: Surface Modificationmentioning

confidence: 99%

Surface modification of Ti6Al4 V implants by heat, H₂O₂ and alkali treatments

Khodaei

Meratian

Shaltooki

et al. 2016

Surface Engineering

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In the present research we have applied three types of surface modifications on Ti6Al4 V alloy including heat treatment, H 2 O 2 treatment and alkali treatment. Scanning electron microscope and thin-film X-ray diffractometry (TF-XRD) were used to analyse the surface structure and the formed phases on the surface modified specimens. In vitro bioactivity evaluations were carried out and the cytocompatibility assay was performed using the evaluation of viability and attachment of L-929 fibroblast cells. The results revealed more bioactivity of the alkali-treated Ti6Al4 V alloy compared to other surface modifications. Better cellular response was also observed on the alkali-treated specimens. According to the results of our study, alkali treatment enhanced the in vitro bioactivity and cytocompatibility of Ti6Al4 V alloy more effectively than H 2 O 2 treatment and heat treatment.

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“…[14,15] Depending on the process parameters, different kinds of CaP coatings can be deposited with variations in chemical composition (HA, hydroxyapatite, OCP, octacalcium phosphate or TCP, tri calcium phosphate), morphology (globules, platelets,. .…”

Section: Surface Modificationmentioning

confidence: 99%

Bone Engineering with Porous Ceramics and Metals

et al. 2011

Self Cite

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The aging of the population of the western countries increasingly necessitate the development of innovative health care approaches including bone replacement and regeneration. The demand for implants is not only intensified but due to the limited life time of these components, an increasing number of implants need revision. Despite the strong research efforts on biomaterials in general, large bone effects are still a big challenge for orthopedic surgeons. Conventionally, bone replacement can be solved by distraction, the use of auto-and allografts or synthetic produced implants. Nevertheless, over the last 20 years intensive research has been performed on a more elegant but more complex new approach called bone tissue engineering. Tissue engineering uses porous scaffolds with properties comparable to trabecular bone. Bone healing is enhanced by seeding these supports with human cells and by the addition of bone growth stimulating molecules. [1] Despite the very successful results obtained on twodimensional materials, it is still waiting on a real reproducible results on three-dimensional scaffolds. A wide variety of materials including ceramics, glass, metals, polymers and composites have been studied to be applied as a porous scaffold material.The self-healing capacity of bone for the reconstruction of small fractures is widely recognized. However, large bone defects still pose a big challenge for orthopedic surgeons. Tissue engineering using porous scaffolds is a new trend to solve this problem and to speed the healing process. When seeded with human cells and bone growth stimulating molecules, they enhance bone healing. Such porous supports try to mimic the properties of trabecular bone. The needed structural properties are: a high and interconnected porosity, pore sizes in the range of 100-500 mm, mechanical properties comparable to trabecular bone and a microporous surface to allow further coating, cell attachment and seeding. Starting from these requirements, it is clear that a cellular material has the ideal architecture for such biomedical scaffold. Polymeric, ceramic or metallic foam structures can be obtained by different manufacturing routes. In our group we optimized three methods, all starting from a powder suspension. They are the PU template technique, gelcasting and the 3D fiber deposition (3DFD) method. Ti and Ti-6Al-4V scaffolds produced by gelcasting and 3DFD can mimic the structural and mechanical properties of the trabecular bone. Hydroxyapatite (HA) and mixtures of hydroxyapatite and beta tricalcium phosphate (b-TCP) were tested for their rate of dissolution in simulated body fluid (SBF) and for their strength as function of their composition. Recently, it was proven that magnesium is a biocompatible and bio-absorbable material. Therefore, as a metallic scaffold it can be expected that it can fulfill both functions of the biomedical scaffold: to be load-bearing and to be bio-absorbable. Nevertheless, the realization of this ideal scaffold needs much more fundamental research. Some preliminar...

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Thermal decomposition of bioactive sodium titanate surfaces

Cited by 25 publications

References 13 publications

Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Surface modification of Ti6Al4 V implants by heat, H₂O₂ and alkali treatments

Bone Engineering with Porous Ceramics and Metals

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Thermal decomposition of bioactive sodium titanate surfaces

Cited by 25 publications

References 13 publications

Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Relationship between valence of titania and apatite mineralization behavior in simulated body environment

Surface modification of Ti6Al4 V implants by heat, H2O2 and alkali treatments

Bone Engineering with Porous Ceramics and Metals

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Product

Resources

About

Surface modification of Ti6Al4 V implants by heat, H₂O₂ and alkali treatments