Physico-chemical considerations of titanium as a biomaterial

Tengvall, Pentti; Lundström, Ingemar

doi:10.1016/0267-6605(92)90056-y

Cited by 325 publications

(217 citation statements)

References 70 publications

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“…The addition of H 2 O 2 to the MEM solution, strongly promotes the formation of a continous nanocomposite layer of HA and amino acids. The reactions at the Ti oxide surface that are stimulated by the presence of H 2 O 2 are complex [15,16], but the end result is the growth of a thicker, continuous but porous nanocomposite layer with an overall composition similar to that formed in pure MEM solution. A schematic diagram of the proposed surface structures which develop after 72 hours immersion in MEM and MEM + H 2 O 2 are shown in Figure 13.…”

Section: Discussionmentioning

confidence: 99%

“…Hence, for Ti alloys, release of H 2 O 2 in the anti-inflammatory response is an important beneficial process as it serves to accelerate osseointegration. For Ti alloy implant surfaces in the body, in addition to amino acids, the extra-cellular material contains important proteins, such a proteoglycans [15,16]. It is to be expected that such proteins in addition to amino acids will become incorporated into the growing HA layer, forming a surface which favours osteoblast growth.…”

Section: Discussionmentioning

confidence: 99%

“…Hydrogen [15,16]. Exposure to H 2 O 2 causes thickening and roughening of the oxide on Ti [17][18][19][20][21].…”

Section: Introductionmentioning

confidence: 99%

“…Tengvall et al [15,16] proposed that the end-product of Ti implanted into the body is the formation of a duplex oxide with a mostly TiO 2 inner layer and stable hydrated TiOOH gel-like oxide outer layer with good ion and protein exchange properties. Proteins, proteoglycans, inorganic ions and other macromolecules will be incorporated into this gel-like outer layer and provide a surface to which fibroblast and osteoblast cells readily attach.…”

Section: Introductionmentioning

confidence: 99%

“…Inserting implants into living tissue causes inflammatory responses with the biological formation of H 2 O 2 and other species in the vicinity of the implant [15,16]. Consequently, immersion of implants in biological solutions with the addition of H 2 O 2 will mimic the environment found for an implant when first inserted into the body.…”

Section: Introductionmentioning

confidence: 99%

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Nanocomposite hydroxyapatite formation on a Ti–13Nb–13Zr alloy exposed in a MEM cell culture medium and the effect of H2O2 addition

et al. 2009

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Section: Discussionmentioning

confidence: 99%

Section: Discussionmentioning

confidence: 99%

“…Hydrogen [15,16]. Exposure to H 2 O 2 causes thickening and roughening of the oxide on Ti [17][18][19][20][21].…”

Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

See 3 more Smart Citations

Nanocomposite hydroxyapatite formation on a Ti–13Nb–13Zr alloy exposed in a MEM cell culture medium and the effect of H2O2 addition

et al. 2009

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Bone-bonding behavior of plasma-sprayed coatings of BioglassR, AW-glass ceramic, and tricalcium phosphate on titanium alloy

Kitsugi

Nakamura

Oka

et al. 1996

J. Biomed. Mater. Res.

127

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The bone-bonding behavior of three kinds of bioactive ceramics coated on titanium alloy by the plasma-spray technique was investigated. Titanium alloy (Ti-6A1-4V) coated with BioglassR (45S5), apatite-wollastonite containing glass ceramic (AW), or beta-tricalcium phosphate (TCP) was prepared, and rectangular specimens were implanted into the tibial bones of mature male rabbits, which were sacrificed 8 or 24 weeks after implantation. The tibiae containing the implants were dissected out and subjected to detachment tests to measure the failure load. The bone-implant interface was investigated by Giemsa surface staining, contact microradiography, and scanning electron microscopy-electron probe microanalysis (SEM-EPMA). Eight weeks after implantation, the failure loads for implants coated with BioglassR, AW, and TCP were 1.04 +/- 0.94, 2.03 +/- 1.17, and 3.91 +/- 1.51 kg, respectively, and 24 weeks after implantation, the respective failure loads were 2.72 +/- 1.33, 2.39 +/- 1.30, and 4.23 +/- 1.34 kg. Failure loads of AW- and TCP-coated implants did not increase significantly with time. After the detachment test, breakage of the coating layer was observed. Bioactive ceramics can act as stimulants that induce bonding between bone and metal implants. However, failure load of metal implants coated with the bioactive ceramics was lower than that of bulk AW or TCP. It appears impossible to obtain a higher failure load using a bioactive-ceramic coating on titanium alloy. Histologically, the coating layer was found to become detached from the metal implant and the bone tissue bonded to the coating layer. SEM-EPMA observation revealed breakage of the coating layer, although bonding between bone and the coating layer was evident. A Ca-P-rich layer was observed at the interface between bone and the AW coating, and a Ca-P-rich and a Si-rich layer were observed at the interface between bone and the BioglassR coating. For clinical application, it would seem better to use coated metal implants for short-term implantation. However, there is a possibility of breakage of the coating layer because of both dissolution of the bioactive ceramic and mechanical weakness at the interface between the coating layer and the metal implant.

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Bone bonding behavior of titanium and its alloys when coated with titanium oxide (TiO2) and titanium silicate (Ti5Si3)

Kitsugi

Nakamura

Oka

et al. 1996

J. Biomed. Mater. Res.

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It has been proposed that the essential requirement for artificial materials to bond to living bone is the formation of bonelike apatite on their surfaces in the body. Recent studies have shown that titanium hydrogel and silica gel induce apatite formation on their surface in a simulated body fluid. In this study, the influence of titanium oxide and titanium silicate on the bonding of titanium alloys to bone was studied. Rectangular implants (15 x 10 x 2.2 mm) of titanium, Ti-6Al-4V, Ti-6Al-2Nb-Ta, Ti-6Al-4V coated with TiO2, and Ti-6Al-4V coated with Ti5Si3 were implanted into the tibial metaphyses of mature rabbits. At 8 and 24 weeks after implantation, the tibiae containing the implants were dissected out and subjected to a detaching testing. The failure load for titanium, Ti-6Al-4V, Ti-6Al-2Nb-Ta, Ti-6Al-4V coated with TiO2, and Ti-6Al-4V coated with Ti5Si3 were, respectively, 0.68 +/- 0.48, 0.22 +/- 0.46, 0.67 +/- 0.59, 2.18 +/- 0.71 and 2.03 +/- 0.41 kgf at 8 weeks, and 2.7 +/- 0.91, 2.58 +/- 1.29, 2.38 +/- 0.41, 3.79 +/- 1.7, and 2.79 +/- 0.87 kgf at 24 weeks after implantation. Histological examination by Giemsa surface staining, CMR, and SEM-EPMA revealed the coated titanium alloy implants directly bonded to bone tissue during early implantation. A Ca-P layer was observed at the interface of the coated implants and the bone. The results of this study indicated that TiO2 and Ti5Si3 can enhance the early bonding of titanium alloys to bone by inducing a Ca-P layer (chemical apatite) on the surface of titanium alloys. It also is suggested that the direct bone contact occurs in relation to the calcium and phosphorus adsorption onto the surface of the titanium passive layer formed during long-term implantation.

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Physico-chemical considerations of titanium as a biomaterial

Cited by 325 publications

References 70 publications

Nanocomposite hydroxyapatite formation on a Ti–13Nb–13Zr alloy exposed in a MEM cell culture medium and the effect of H2O2 addition

Nanocomposite hydroxyapatite formation on a Ti–13Nb–13Zr alloy exposed in a MEM cell culture medium and the effect of H2O2 addition

Bone-bonding behavior of plasma-sprayed coatings of BioglassR, AW-glass ceramic, and tricalcium phosphate on titanium alloy

Bone bonding behavior of titanium and its alloys when coated with titanium oxide (TiO2) and titanium silicate (Ti5Si3)

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