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![Biomedical applications of titanium and its alloys [10].](profile/Agnieszka-Stroz/publication/322516421/figure/fig1/AS:665363310211072@1535646383275/Fig-1-Biomedical-applications-of-titanium-and-its-alloys-10.png)
Biomedical applications of titanium and its alloys [10].
![Fig. (1). Biomedical applications of titanium and its alloys [10].](profile/Agnieszka-Stroz/publication/322516421/figure/fig1/AS:665363310211072@1535646383275/Fig-1-Biomedical-applications-of-titanium-and-its-alloys-10_Q320.jpg)
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... biomaterials are used as bone implant in differ- ent parts of the body [1][2][3][4][5]. Titanium and its alloys are most often used as biomaterials due to the high strength and rela- tively high Young modulus. Fig. (1) schematically shows possible biomedical applications of titanium and its ...
Context 2
... biomaterials are used as bone implant in differ- ent parts of the body [1][2][3][4][5]. Titanium and its alloys are most often used as biomaterials due to the high strength and rela- tively high Young modulus. Fig. (1) schematically shows possible biomedical applications of titanium and its ...
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Citations
... One of the answers to the challenges of modern medicine is the development of new biomaterials with increased corrosion resistance and biocompatibility, intended for longterm implants in implantology [1][2][3]. The most promising group of biomaterials for such applications is titanium and its single-phase alloys α or β and two-phase alloys α + β, which contain the additions of Al, V, Nb, Ta, Zr, Mo, Si, Sn, Pd, Fe, and Hf and exhibit osseointegrative properties [1][2][3][4][5][6][7][8][9][10][11]. The two-phase Ti-6Al-4V alloy has so far dominated the long-term implant market. ...
... The area of mutual bone adhesion to the porous surface of the implant is also increased. This is why almost all new generation implants have a porous surface, obtained with the use of various technologies [1][2][3][5][6][7][8][9][10][12][13][14][15][16][17][18][19][20][21][22]. ...
... Self-organized ONT layers on titanium and its alloys are produced by anodization, usually at a constant voltage in the range of 1-30 V in aqueous electrolytes or 5-150 V in non-aqueous electrolytes with the addition of fluoride ions (0.1-1 wt%) [6][7][8][9][10][12][13][14][15][16][18][19][20][21][23][24][25]. During this electrochemical oxidation process carried out in electrolytes containing fluoride ions on the anode surface, the oxidation and dissolution of metal oxides take place. ...
This work concerns the development of a method of functionalization of the surface of the biomedical Ti–6Al–7Nb alloy by producing oxide nanotubes (ONTs) with drug-eluting properties. Shaping of the morphology, microstructure, and thickness of the oxide layer was carried out by anodization in an aqueous solution of 1 M ethylene glycol with the addition of 0.2 M NH4F in the voltage range 5–100 V for 15–60 min at room temperature. The characterization of the physicochemical properties of the obtained ONTs was performed using SEM, XPS, and EDAX methods. ONTs have been shown to be composed mainly of TiO2, Al2O3, and Nb2O5. Single-walled ONTs with the largest specific surface area of 600 cm2 cm−2 can be obtained by anodization at 50 V for 60 min. The mechanism of ONT formation on the Ti–6Al–7Nb alloy was studied in detail. Gentamicin sulfate loaded into ONTs was studied using FTIR, TG, DTA, and DTG methods. Drug release kinetics was determined by UV–Vis spectrophotometry. The obtained ONTs can be proposed for use in modern implantology as carriers for drugs delivered locally in inflammatory conditions.
In the group of vanadium-free titanium alloys used for applications for long-term implants, the Ti-13Zr-13Nb alloy has recently been proposed. The production of a porous layer of oxide nanotubes (ONTs) with a wide range of geometries and lengths on the Ti-13Zr-13Nb alloy surface can increase its osteoinductive properties and enable intelligent drug delivery. This work concerns developing a method of electrochemical modification of the Ti-13Zr-13Nb alloy surface to obtain third-generation ONTs. The effect of the anodizing voltage on the microstructure and thickness of the obtained oxide layers was conducted in 1 M C2H6O2 + 4 wt% NH4F electrolyte in the voltage range 5–35 V for 120 min at room temperature. The obtained third-generation ONTs were characterized using SEM, EDS, SKP, and 2D roughness profiles methods. The preliminary assessment of corrosion resistance carried out in accelerated corrosion tests in the artificial atmosphere showed the high quality of the newly developed ONTs and the slight influence of neutral salt spray on their micromechanical properties.
Solvents are widely used in organic synthesis. Sulfolane is a five-membered heterocyclic organosulfur sulfone (R-SO2-R’, where R/R’ is alkyl, alkenyl, or aryl) and an anthropogenic medium commonly used as industrial extractive solvent in the liquid-liquid and liquid-vapor extraction processes. Under standard conditions sulfolane is not aggressive towards steel, but at higher temperatures and in oxygen, water, or chlorides presence, it can be decomposed into some corrosive (by-)products with generation of SO2 and subsequent formation of corrosive H2SO3. This pilot-case study provides data from laboratory measurements performed in low conductivity sulfolane-based fluids using an industrial multi-electrochemical technique for reliable detection of corrosion processes. In particular, a comprehensive evaluation of the aqueous phase impact on general and localized corrosion of AISI 1010 carbon steel in sulfolane is presented. Assessment of corrosive damage was carried out using an open circuit potential method, potentiodynamic polarization curves, SEM/EDS and scanning Kelvin probe technique. It was found that an increase in the water content (1–3 vol.%) in sulfolane causes a decrease in the corrosion resistance of AISI 1010 carbon steel on both uniform and pitting corrosion due to higher conductance of the sulfolane-based fluids.
