Porous titanium implant materials and their potential in orthopedic surgery

Schuh, Alexander; Luyten, J.; Vidael, R.; Hönle, Wolfgang; Schmickal, Thomas

doi:10.1002/mawe.200700246

Cited by 12 publications

(11 citation statements)

References 16 publications

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“…Regarding the stiffness value for cortical bone replacement (approximately 20 GPa), Figure 8 [2,10,14,[31][32][33][34] shows that the best results (20 to 25 GPa) were obtained for the lowest compacting pressure (38.5 MPa) with sintering temperatures of 1273 K and 1373 K (1000°C and 1100°C). These conditions correspond to the highest porosity (roughly 30 pct) in the middle part of the cylindrical samples.…”

Section: Mechanical Testingmentioning

confidence: 95%

Conventional Powder Metallurgy Process and Characterization of Porous Titanium for Biomedical Applications

Torres

Pavón

Nieto

et al. 2011

Metall Mater Trans B

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Commercially pure titanium (c.p. Ti) is one of the best metallic biomaterials for bone tissue replacement. However, one of its main drawbacks, which compromises the service reliability of the implants, is the stress-shielding phenomenon (Young's modulus mismatch with respect to that one of the bone). Several previous works attempted to solve this problem. One alternative to solve that problem has been the development of biocomposites implants and, more recently, the fabrication of titanium porous implants. In this work, porous samples of c.p. Ti grade 4 were obtained using conventional powder metallurgy technique. The influence of the processing parameters (compacting pressure and sintering temperature) on the microstructure features (size, type, morphology, and percentage of porosity), as well as on the mechanical properties (compressive yield strength, and conventional and dynamic Young's modulus) were investigated. The results indicated that there is an increment in density, roundness of pores, and mean free path between them as compacting pressure and/or sintering temperature is increased. The Young's modulus (conventional and dynamic) and yield strength showed the same behavior. Better stiffness results, in the central part of cylindrical samples, were obtained for a uniaxial compression of 38.5 MPa using a sintering temperature of 1273 K and 1373 K (1000°C and 1100°C). An evaluation of porosity and Young's modulus along a cylindrical sample divided in three parts showed that is possible to obtain a titanium sample with graded porosity that could be used to design implants. This approach opens a new alternative to solve the bone resorption problems associated with the stress-shielding phenomenon.

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Section: Mechanical Testingmentioning

confidence: 95%

Conventional Powder Metallurgy Process and Characterization of Porous Titanium for Biomedical Applications

Torres

Pavón

Nieto

et al. 2011

Metall Mater Trans B

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“…The need for a metallic implant material combining superelasticity with a biocompatibility comparable to that of pure titanium represents the main incentive for ongoing research in the field of -type Ti-based superelastic alloys [1]- [6]. Ternary and quaternary Ti-Nb-based alloys have been extensively investigated over the last ten years and the results confirm the possibility of producing Ni-free, Ti-based alloys with superelasticity thanks to reversible to α′′ martensitic transformation [7].…”

Section: Introductionmentioning

confidence: 90%

Mechanical properties of porous metastable beta Ti–Nb–Zr alloys for biomedical applications

Braïlovski

Прокошкин

Gauthier

et al. 2013

Journal of Alloys and Compounds

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Mechanical properties of porous metastable beta Ti-Nb-Zr alloys for biomedical applications Braïlovski, V.; Prokoshkin, S.; Gauthier, M.; Inaekyan, K.; Dubinskiy, S. melting. The obtained ingots were divided into two batches: the first subjected to cold rolling (CR) from 30 to 85% of thickness reduction, and subsequent annealing in the 450 to 600°C temperature range (1h). Regardless of the CR intensity, Ti-Nb-Zr samples subjected to 600°C annealing showed the highest fatigue resistance during roomtemperature cumulative cycling due to the stress-induced martensitic transformation occurring in the polygonized dislocation substructure (average subgrain size ∼ 100 nm). The second batch was atomized to produce 100-micronsize powders in order to manufacture open-cell porous material (cell size vary from 136 to 561 microns) of 46% porosity by means of powder metallurgy using a polymer-based foaming process. Tensile, compression and bending testing were performed at RT on foam samples annealed at 450 to 600°C (1h). Results indicated that Young's modulus of Ti-Nb-Zr foams significantly decreases as compared to the as-sintered material: when annealing temperature increases from 450 to 600°C, Young's modulus decreases from 10±2 GPa to 6±1 GPa. Under the same testing conditions, Ti-CP foams produced by the same technology and having similar porosity remain fairly insensible to post-sintering annealing.

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“…[35] Plateau stresses of 30-65 MPa and Young's modulus of 1.2-2.8 GPa were reported for commercial Ti foams with 70-80% porosity produced by a solid sacrificial template. [36] Ti foams prepared by slip casting of particle stabilized emulsions showed yielding strengths of 141 AE 5.7 and 121 AE 5.4 MPa for samples with a porosity of 56.1 and 65.2%. [37] In this study, the 250 mm pore sized Ti foams with 55% porosity shows plateau stress of 45.1 AE 3.0 MPa and Young's modulus of 13.46 AE 1.4 GPa.…”

Section: Mechanical Propertiesmentioning

confidence: 99%

Spark Plasma Sintering, Microstructures, and Mechanical Properties of Macroporous Titanium Foams

2010

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Porous materials with interconnected porosity have widespread applications in many fields of engineering. [1] Bulk porous metallic materials (honeycomb, foam, and hollow spheres) are known for their interesting combinations of the advantages of a metal (strong, hard, tough, electrically, and thermally conductive, etc.) with the functional properties of porous structures (lightweight with adjustable properties by selecting the density. [2] Because of this, porous metals are interesting for a number of engineering applications such as structural panels, energy absorption devices, acoustic damping panels, compact heat exchangers, and biomedical implants etc. [3] Porous titanium (Ti) and its alloy were widely used in the biomedical field due to their outstanding mechanical properties, low density, chemical resistance, and biocompatibility. As a kind of long-term load-bearing implant, the porous structures of Ti and its alloy could lead to a reliable anchoring of host tissue into the porous structure, and allow mechanical interlocking between bone and implant. [4] The ingrowths of bone into the porous structure could ensure a good transfer of mechanical forces. Therefore, a porous structure is preferable for the Ti and its alloys using as bone scaffolds.However, porous Ti and its alloys are difficult to be produced from the liquid state, due to the high melting point, the high reactivity at high temperature above 1000 8C and the contamination susceptibility. Thus, fabrication processes for porous Ti has to date focused on the powder metallurgy (PM) route and avoided the liquid route. [5] Many techniques have been applied to produce porous Ti and its alloy implants in recent years. [6][7][8][9][10] Nevertheless, there are still problems to be solved in the field of porous Ti for biomedical applications [11] : the difficulty to create controlled porosity and pore sizes, the insufficient knowledge of porous structureproperty relationships, the requirements of new sintering techniques with rapid energy transfer, and less energy consumption and so on.Spark plasma sintering (SPS) as one of the field assisted sintering techniques, is a relative new sintering technique for PM and ceramics. SPS is a high efficient and energy saving powder consolidation and sintering technology capable of processing conductive and non-conductive materials. [12] However, most of SPS researches were performed on dense materials; fewer studies were on porous materials. [13] The SPS studies on porous Ti alloys were mainly using low temperature and low pressure to decrease the relative density of samples. [14][15][16][17][18][19] The samples exhibited pore sizes of some tens of micrometers and a porosity in the range of 20-45%. As bone foams, high porosity (>50%) and macropore size (>200 mm) are essential requirements for the bone growth and the osteoconduction. [20,21] Macroporous nanostructured tricalcium phosphate scaffolds have been successfully COMMUNICATION [*] Dr. for his support in mechanical testing.Macroporous pure titanium (Ti) foams with...

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Porous titanium implant materials and their potential in orthopedic surgery

Cited by 12 publications

References 16 publications

Conventional Powder Metallurgy Process and Characterization of Porous Titanium for Biomedical Applications

Conventional Powder Metallurgy Process and Characterization of Porous Titanium for Biomedical Applications

Mechanical properties of porous metastable beta Ti–Nb–Zr alloys for biomedical applications

Spark Plasma Sintering, Microstructures, and Mechanical Properties of Macroporous Titanium Foams

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