“…Unlike traditional methods, this method does not require the use of toxic solvents to remove residues, because the porous structure formed is mainly composed of crystalline phases of Na 2 Ti 6 O 13 /TiO 2 reported as biocompatible [14,18] with adequate chemical stability [[12], [13], [14], [15]]. Another advantage of this method was the porosity and roughness control by varying the amount of NaHCO 3 and the sintering time [19]. Fig.…”
“…Unlike traditional methods, this method does not require the use of toxic solvents to remove residues, because the porous structure formed is mainly composed of crystalline phases of Na 2 Ti 6 O 13 /TiO 2 reported as biocompatible [14,18] with adequate chemical stability [[12], [13], [14], [15]]. Another advantage of this method was the porosity and roughness control by varying the amount of NaHCO 3 and the sintering time [19]. Fig.…”
“…13 After implantation in vivo, poor bioactivity of the biomaterial can cause inferior bone regeneration and osseointegration, which might reduce the initial fixation and long-term stability of the implant. 14 Bioactive materials (eg, bioactive bioglass/ceramic) possess the ability to promote NB formation and osseointegration with host bone tissue. 14,15 However, these inorganic bioactive materials exhibit low toughness because of their brittleness, making it difficult to repair load-bearing bone defects.…”
Section: Introductionmentioning
confidence: 99%
“…14 Bioactive materials (eg, bioactive bioglass/ceramic) possess the ability to promote NB formation and osseointegration with host bone tissue. 14,15 However, these inorganic bioactive materials exhibit low toughness because of their brittleness, making it difficult to repair load-bearing bone defects. Synthetic NDPs (eg, PA, PE, and PEEK) possess outstanding mechanical properties and machinability, as well as easy processing.…”
Introduction: Polyimide (PI) exhibits good biocompatibility and high mechanical strength, but biological inertness that does not stimulate bone regeneration, while laponite possesses excellent bioactivity. Methods: In this study, to improve the bioactivity of PI, nano-laponite ceramic (LC)-PI composites (LPCs) were fabricated by melt processing as implantable materials for bone repair. Results: The compressive strength, hydrophilicity, and surface roughness of LPCs with 40 w % LC content (LPC40s) were higher than LPC20s, and LPC20s higher than pure PI. In addition, no apatite mineralization occurred on PI, while apatite mineralized on LPCs in simulated body fluid. Compared with LPC20, more apatite deposited on LPC40, indicating good bioactivity. Moreover, the adhesion, proliferation, and alkaline phosphatase activity of rat bone mesenchymal stem cells on LPCs significantly increased with LC content increasing in vitro. Furthermore, the evaluations of animal experiments (micro-CT, histology, and pushout load) revealed that compared with LPC20 and PI, LPC40 significantly enhanced osteogenesis and osseointegration in vivo. Discussion: Incorporation of LC into PI obviously improved not only surface physicochemical properties but also biological properties of LPCs. LPC40 with high LC content displayed good biocompatibility and bioactivity, which markedly promoted osteogenesis and osseointegration. Therefore, with its superior biocompatibility and bioactivity, LPC40 could be an alternative candidate as an implant for orthopedic applications.
“…Moreover, annealing the coating is to obtain nanostructured coatings with pre-determined structure, chemical and phase composition [16]. Other publications have also discussed the proper temperature to improve the strength and quality of the titanium-hydroxyapatite interface in the annealing temperature range of 500 -750 C [17][18][19][20]. However, at the high annealing temperature, the values of thermal expansion coefficients of Ti alloy and TiO2, as well as those of HAp and TiO2 should be concerned carefully.…”
In this study, TiO2 nanostructured coatings on Ti-6A-4V alloys were fabricated by two methods: H2O2 oxidation and RF sputtering. In the annealing temperature range of 25 C - 500 C, there were the peaks at 35, 37, 40 and 52 corresponding to {100}, {002}, {101} and {102} crystal planes of hcp structure of α-Ti. At the annealing temperature of 600 C, there was the presence of peaks corresponding to crystal planes of anatase and rutile TiO2. The relative intensities of anatase and rutile phases of the sample fabricated by RF sputtering were 3.62 and 10.25 %, respectively; while those of the sample fabricated by H2O2 oxidation were 21.27 and 3.20 %, respectively (The relative intensity of α-Ti phase was 100 %). The results investigated the peak shift of α-Ti phase in TiO2/Ti-6Al-4V nanostructured coatings fabricated by the two methods which was reasonably explained from the difference in the thermal expansion coefficients of Ti alloy and TiO2 components, as well as the difference in the ratio of anatase to rutile phases.
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