Introduction

Oshida, Yoshiki

doi:10.1016/b978-008045142-8/50001-3

Cited by 23 publications

(43 citation statements)

References 1 publication

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“…This property could be the reason why Ti-Ag alloys are not anti-bacterial or bactericidal. Titanium alloys are known to easily form a titanium oxide layer on the surface 29) ; thus silver atoms in the alloys might be embedded and/or surrounded by the oxide layer, and seldom released from the surface. However, as discussed above, the property of the titanium surface can be modified by the addition of silver in terms of bacterial adhesion and colonization.…”

Section: Discussionmentioning

confidence: 99%

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

et al. 2014

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Titanium-silver (Ti-Ag) alloy has been improved for machinability and mechanical properties, but its anti-biofilm properties have not been elucidated yet. Thus, this study aimed to evaluate the effects of Ti-Ag alloy on biofilm formation and bacterial viability in comparison with pure Ti, pure Ag and silver-palladium (Ag-Pd) alloy. Biofilm formation on the metal plates was evaluated by growing Streptococcus mutans and Streptococcus sobrinus in the presence of metal plates. Bactericidal activity was evaluated using a film contact method. There were no significant differences in biofilm formation between pure Ti, pure Ag and Ag-Pd alloy, while biofilm amounts on Ti-20% Ag and Ti-25% Ag alloys were significantly lower (p<0.05). In addition, Ti-Ag alloys and pure Ti were not bactericidal, although pure Ag and Ag-Pd alloy killed bacteria. These results suggest that Ti-20% Ag and Ti-25% Ag alloys are suitable for dental material that suppresses biofilm formation without disturbing healthy oral microflora.

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Section: Discussionmentioning

confidence: 99%

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

et al. 2014

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“…[14] Plasma atomized CpTi spherical powder (-180 lm, 0.12 wt.% oxygen) was admixed with a polyethylene wax powder and a chemical foaming agent (p,p′-oxybis[benzenesulfonyl hydrazide]). The resulting powder mixture was transferred into a mold and foamed at 210°C in air.…”

Section: Methodsmentioning

confidence: 99%

“…2-7 nm) and confirms that the oxide was mostly formed at low temperature when the vacuum furnace was opened to air at the end of the treatment. [7] Since the specific surface area of the foam is high, the contribution of this thin oxide film is significant and must be extracted from the global oxygen content of the foam to determine the contribution of the oxygen in solution. In the present study, the amount of oxygen in solution in titanium foams was determined by subtracting the surface contribution as calculated in Figure 6 (0.06 wt%O) to the total amount of oxygen determined using inert gas fusion techniques.…”

Section: Fig 6 Oxygen Pick-up Measured Using A) Weigh Gain and B) Tmentioning

confidence: 99%

“…Using high temperature microscopy, S.Malinov et al presented the in situ formation of the oxide and its dissolution when titanium alloy specimens were treated at high temperature. [7] After its dissolution, an oxide layer is re-formed on the titanium surface when exposed to oxygen at lower temperature, where oxygen diffusivity is low. Accordingly, the cycling between high and low temperature or between dissolution and reformation of the oxide layer inevitably lead to an increase of the total amount of oxygen in the material.…”

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confidence: 99%

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Effect of Oxygen Concentration and Distribution on the Compression Properties on Titanium Foams

Lefebvre¹,

Baril²

2008

Adv Eng Mater

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The effect of oxygen in solution and surface oxide on the properties of titanium foams under compression is discussed in this report. The authors present a simple method to discriminate the amount of oxygen coming from the oxide and from the solid solution. Oxygen in solution has an impact on the hardness, yield strength and ductility while surface oxide has little impact on the compression properties within the concentration evaluated.

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“…Therefore, it produces a much better direct contact with the bone. Figure 11 shows the distribution of surface roughness of the successfully implanted materials, 28) along with those of SW/mirror and SW/FPB. The surface roughness of SW/ FPB is nearly equal to that of a polished surface and is located within the region required for successful implantation, while that of SW/mirror, with a surface roughness less than 0.1 µm is outside of this region.…”

Section: Bone Contactabilitymentioning

confidence: 99%

Change in Mechanical Strength and Bone Contactability of Biomedical Titanium Alloy with Low Young’s Modulus Subjected to Fine Particle Bombarding Process

et al. 2015

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Beta-type Ti-29Nb-13Ta-4.6Zr (TNTZ), which is a recently developed biomedical titanium alloys, shows a relatively low Young's modulus of around 60 GPa when subjected to a solution treatment.However, our focus in this study was on the practical applications of TNTZ in vivo because its mechanical strength decreases with solution treatment progress. Therefore, we investigated the effect of fine particle bombarding (FPB) on the mechanical properties of TNTZ subjected to a cold-swaging treatment in order to maintain its relatively low Young's modulus and to improve its mechanical properties. The relative bone contact ratios between the cancellous bones of Japanese white rabbits and column-shaped TNTZ samples subjected to FPB were also evaluated.The microstructure of cold-swaged TNTZ showed a single beta-phase with a marble-like structure. Moreover, its Vickers hardness did not increase remarkably with changes in its diameter, although the average diameter of the beta-grains of solutionized TNTZ ranged from 5.0 to 20 µm, depending on the increase in the holding time of the solution treatment. The Vickers hardness and Young's modulus of TNTZ subjected to FPB increased at the edge of the specimen surface to be around 70% and 15%, respectively, more than those of cold-swaged TNTZ. Further, the fatigue strength of TNTZ subjected to FPB became significantly higher than that of cold-swaged TNTZ in the high-cycle fatigue life region. Lastly, TNTZ with a rough surface texture (Ra: 0.65 µm) showed a relative bone contact ratio of more than 80% after undergoing FPB; this value was significantly higher than that of cold-swaged TNTZ with a very smooth surface texture (Ra: 0.07 µm).

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Introduction

Cited by 23 publications

References 1 publication

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

Effect of Oxygen Concentration and Distribution on the Compression Properties on Titanium Foams

Change in Mechanical Strength and Bone Contactability of Biomedical Titanium Alloy with Low Young’s Modulus Subjected to Fine Particle Bombarding Process

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Introduction

Cited by 23 publications

References 1 publication

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

Inhibitory effect of Ti-Ag alloy on artificial biofilm formation

Effect of Oxygen Concentration and Distribution on the Compression Properties on Titanium Foams

Change in Mechanical Strength and Bone Contactability of Biomedical Titanium Alloy with Low Young&rsquo;s Modulus Subjected to Fine Particle Bombarding Process

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Product

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Change in Mechanical Strength and Bone Contactability of Biomedical Titanium Alloy with Low Young’s Modulus Subjected to Fine Particle Bombarding Process