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Titanium is very resistant to corrosion as a result it can be passivated by thin layer of titanium oxide which is formed instantly on its surface.
If left unchecked this oxide layer can become thicker over time. With the exception of pure titanium, the modulus of elasticity of Ti-6Al-4V is closer to that of bone than that of any other widely used metallic implant biomaterial. Ti alloys are able to maintain the fine balance between sufficient strength to resist fracture under occlusal forces and to retain a lower modulus of elasticity for more uniform stress distribution across the bone implant interface 5. Titanium is considered to be a biocompatible material.
However, in light of recent clinical reports regarding contact dermatitis or granulomatous reactions to titanium upon its use in pacemakers, hip prostheses, surgical clips, or osteosynthesis, there is debate with regard to titanium allergies. In addition, titanium has also been reported to possibly cause generalized health problems, and the potential for adverse human tissue responses to titanium dioxide, which always covers the surface of titanium materials, has been reported.
Chronic low-level metal exposure may occasionally result in metal sensitization and undesirable side effects. Dental implants, which were purported by the manufacturer to be made of ASTM grade I high-purity titanium It appears that in rare circumstances, for some patients, the titanium used in dental implants may induce an allergic reaction CERAMICS Implant research has focused on discovering tooth colored implant material that improves the aesthetic appearance of dental implants and at the same time is highly biocompatible and able to withstand the forces present in oral cavity.
Ceramic implants can withstand only relative low tensile or shear stress induced by occusal loads, but they can tolerate quite high levels of compressive stress. Ceramics can either be plasma sprayed or coated on to the metallic surfaces which can be more thermodynamically stable, hydrophilic, and non conductive of heat and electricity, thereby producing a high strength integration with bone 5.
Aluminium oxide Al2O3 is used as a standard biomaterial for ceramic implants because of its inertness Biostability with no evidence of adverse in vivo reactions.
Zirconia ZrO2 has also demonstrated a high degree of inertness, although alumina has higher surface wettability compared with other surfaces, such as those of metallic implants. These types of ceramic implants are not bioactive in that they do not promote the formation of bone 5.
Aluminium oxide Al2O3 dental implants osseointegrated well but was withdrawn from market because of its poor survival rate. This combination of favorable mechanical properties makes zirconia a unique and stable material for use in high load situations Surface treatment such as airborne particle abrasion and hand grinding have been found to improve flexural strength of zirconia implant.
The uniaxial strength of zirconia has been found to be MPa. Along with the strength, the fracture toughness is one of the first parameters to evaluate performance of a dental ceramic. Fracture toughness for zirconia implant has been found to be These materials are nonimmunogenic and biocompatible with host tissues. The two most commonly used calcium phosphates are Hydroxyapatite HA and tricalcium phosphate which is used as bone graft material to serve as template for new bone formation, because these materials promote and achieve direct bond of implant to hard tissues.
Both also promote vertically directed bone growth as well as relatively strong bond to bone. Studies have shown that after 4 weeks of implantation, osteocytes accumulate adjacent to HA granules, indicating possibility of osteogenesis with implants. The more crystalline the HA coating the more resistant they are to clinical dissolution. Heat treatment after deposition process improves the crystallinity of HA.
Despite their favorable osteo inductive ability they are also very brittle which makes them unsuitable for use of some stress bearing implant application. These materials are known to form a carbonated hydroxyapatite layer in vivo as a result of their calcium and phosphorus content. The formation of this layer is initiated by migration of calcium, phosphate, sodium and silica ions into the tissue as result of external pH changes.
As elements are released silica rich layer and calcium —phosphorus layer is formed on the surface that stimulates osteoblasts to proliferate. More often they are used as grafting materials for ridge augmentation or bony defects than as a coating material for metallic implant because the interface 5.
Lesser plaque accumulation has been reported with zirconia implants. Bacteria such as S sanguis, Porphyromonas gingivalis, short rods, and cocci have shown lesser adherence to zirconia than to titanium surface. The adhesion of Streptococcus to zirconia has also been shown to similar to that to glass ceramics. There seems to be no difference between polished and glazed zirconia as far as adherence of bacteria is concerned The titanium foam is made by mixing titanium powder with a polymer, and then adding foaming agents that expand the polymer when heated.
Later, through a high-temperature heat treatment, the polymer is removed and the titanium particles are consolidated to provide mechanical strength to the porous structure. The rough surface creates friction between the implant and the bone, and also allows bone growth into the pores to help fix the implant in place.
Among its potential benefits, titanium foam could make dental implants less invasive The new material is composed of the two elements titanium and zirconium. This binary TiZr alloy has a significantly increased mechanical stability compared to titanium grade 4 with respect to elongation.
Sand blasted, acid etched and then stored in 0. Polymers have lower strengths and lower elastic moduli and higher elongations to fracture compared with other classes of biomaterials they are thermal and electrical insulators and are relatively resistant to biodegradation. When compared with bone they have lower elastic moduli with magnitudes closer to soft tissues. Polymers have been fabricated in porus and solid forms for tissue attachment, replacement and augmentation and as coatings for force transfer to soft tissue and hard tissue regions.
In general, polymers and composites of polymers are especially sensitive to sterilization and handling techniques. If intended for implant use, most cannot be sterilized by steam or ethylene oxide. More polymeric biomaterials have electrostatic surface properties and tend to gather dust or other particulate if exposed to semi clean oral environments Vitreous Carbon elicits a very minimal response from host tissues, is one of the most common implant biomaterial.
Thus, carbon deforms at the rate similar to those tissues, enhancing the transmission of biomechanical forces. However carbon is susceptible to fracture under tensile and stress condition because of its brittleness and susceptibility to fracture under tensile stress in the presence of surface flaws, which is usually generated as component of flexural loading 5. Vitreous carbon is a This modulus is similar to that of dentin; this is a significant factor in reducing shearing forces at the implant bone interface.
This implant is formed by molding resin into the implant shape, heat treating it under nitrogen and then vacumizing it to evaporate the nitrogen, oxygen, hydrogen and any impurities included in the resin