Porous Metals as a Hard Tissue Substitute. Part II. Porous Metal Properties

Wheeler, K.R.; Marshall, R.P.; Sump, K. R.

doi:10.3109/10731197309118546

Cited by 7 publications

(2 citation statements)

References 2 publications

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“…VMC consists of a Ti-6A1-4V alloy with interconnecting and controlled porosity achieved through special fabrication techniques. 5 The voids can be varied precisely in shape (for example, spheres or cylinders) or orientation to alter the mechanical and physical properties of the metal as well as the structure of the metal-tissue interface. The ultimate compressive strength of 50% dense VMC (that is, a density of 0.5 times that of the solid alloy) is -30,000 psi.…”

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Development and Evaluation of Porous Dental Implants in Miniature Swine

et al. 1976

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Organized bone ingrowth in endosteal porous implants fabricated from VMC titanium alloy and surgically implanted with a tight interference fit, securely anchored the implants in fresh and healed mandibular premolar sites of miniature swine. This bone-implant union retained its integrity under high as well as slight masticatory stresses up to one-year after implantation. Bone invasion of the alumina porcelain implants was impeded by the lack of adequate interconnecting porosity; when the porosity was increased, insufficient ceramic strength prohibited a tight initial bone-implant fit. As a consequence, inadequate initial implant stability resulted in a soft tissue encapsulation of the majority of the ceramic implants. Histological examination and mechanical testing results were similar for bone-ingrown implants exposed to different experimental stresses for 4, 5, 8, and 12 months. Bone ingrowth and interface shear strengths were also similar in the different VMC pore sizes and shapes investigated. The design of intraoral attachments appeared critical, at least in swine where no postoperative treatment was administered. Gingival inflammation and alveolar bone resorption caused by calculus were severe around truncated cone-shaped devices. Slender transgingival posts, occlusal caps, and crown restorations were less susceptible to calculus accumulation, resulting in a more satisfactory gingival and subgingival response. Excessive epithelial invagination was a problem only in implants with transgingival truncated cones. Good adherence of soft tissue to metal under the gingival mucosa prevented epithelial migration around implants with other transgingival devices. Alveolar bone resportion around the tops of bone-ingrown implants was minimal at the time intervals examined (up to one year); however, a definite conclusion should be delayed until longer-term implants under full occlusion are evaluated.

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Development and Evaluation of Porous Dental Implants in Miniature Swine

et al. 1976

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“…Titanium substrates were coated by plasma-spraying of titanium hydride powders [6]; atomized spherical cast cobaltchromium alloy powders were applied to a metal substrate by aqueous slurry coating and subsequent sintering [7] ; stainless steel AISI 316 L powders were isostatically compacted [8]; "void metal composites" were developed by mixing titanium powder with a metal powder with a low melting point, which vaporized upon sintering [9] ; fine titanium wires [10] and stainless steel AISI 3t6 L [11] were compacted either uniaxially or isostatically. Much attention was paid to producing a sufficiently large pore size, since it had been shown that viable bone ingrowth only occurred when the mean pore size was at least 50#m [12,131. The assessment of some mechanical and especially the elastic properties of the porous structures for bone ingrowth is, however, as important from several points of view.…”

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The mechanical behaviour of porous austenitic stainless steel fibre structures

1978

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The mechanical properties of metal fibre porous structures were studied in the light of their potential application as surface coatings of implants. Stainless steel AISI 316 L fibres with diameters of 50 and 100 #m were compacted and sintered. The variation of the modulus of elasticity with density, as obtained in tension, corresponds closely with theoretical models. The ultimate failure of the tensile specimens proceeds through the fibres, and not through the sinter bonds, except at lower densities. Differences in yield strength between 50 and 100/am fibre tensile specimens are explained on the basis of the onset of plastic deformation of the individual fibres. Upon compression the modulus of elasticity is nearly 10 times smaller than in tension. This result is due to the different deformation patterns of the fibres in compression and tension.

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Key references in biomaterials: Bone/biomaterial interface in orthopedic joint implants

Gruen

Sarmiento

1984

J. Biomed. Mater. Res.

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Porous Metals as a Hard Tissue Substitute. Part II. Porous Metal Properties

Cited by 7 publications

References 2 publications

Development and Evaluation of Porous Dental Implants in Miniature Swine

Development and Evaluation of Porous Dental Implants in Miniature Swine

The mechanical behaviour of porous austenitic stainless steel fibre structures

Key references in biomaterials: Bone/biomaterial interface in orthopedic joint implants

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