synthesis of cdHAp took a shorter time than by other available methods. The
authors have confirmed the formation of 16–39 nm long and 7–16 nm thick
needle-like nanocrystallites.
Murugan et al. [51] also applied microwaves for the synthesis of carbonated
HAp (cHAp) with structural and chemical similarities to biological apatite. Its
bioresorbable nature was determined by its in vitro solubility under physiological
conditions and was found to be higher than that of HAp.
cHAp nanospheres for tissue engineering scaffolds have been prepared by Zhou
and his group [59] using a nanoemulsion method. Nanoemulsions are a new class of
emulsions having very fine and uniform droplet sizes, usually in the range of
20–200 nm [60]. Using this method, microemulsion-like dispersions can be
obtained using very low surfactant concentrations, or even without any surfactant.
Using this method, nanosized, B-type cHAp particles of spherical shape have been
synthesized [59].
Landi et al. [61] have synthesized Mg-doped HAp by a wet-chemical method
and 5.7 mol% Mg-doped HAp showed the best result in biological applications. No
genotoxicity, carcinogenicity, or cytotoxicity was observed using these materials,
which makes them biocompatible. Mg-doped HAp also showed superior material
resorption and better osteoconductivity than stoichiometric HAp.
HAp has excellent biocompatibility, osseointegration, and biostability [9, 10].
Additionally, its unique characteristic of osteoconduction [11–14] in host osseous
materials has been employed in dental implants [62–66] and in bone cement
applications [67–69]. HAp-based implants are made both from natural products
like animal bones or corals, and also from synthetic HAp. The use of HAp
materials made from animal bones are advantageous because they inherit some
properties such as chemical composition and structure from the raw material
[70–72]. In spite of these advantages, HAp-based implants from synthetic HAp
are preferable because of their uniform composition, high biocompatibility,
overall safety, and their completely controllable microstructure [73]. The
limitations of an HAp implant include its hardness and brittleness, which
makes it difficult to shape in the complex forms required for bone treatment,
and its easy migratory tendency from the implanted sites. To overcome these
limitations, many efforts have been made towards development of novel HAp/
organic polymer composites [74]. In the early 1980s, Bonfield introduced the
concept of using bioactive HAp particles/modified polymer composites as
implant materials for bone replacement [75]. Since then, HAp-modified
polymer-based biocomposites have been widely studied for bone tissue replacement. In the next section, we discuss the use of polymers and give a brief
introduction to these polymers and different methods for their preparation.
148
A. Bhowmick et al.
authors have confirmed the formation of 16–39 nm long and 7–16 nm thick
needle-like nanocrystallites.
Murugan et al. [51] also applied microwaves for the synthesis of carbonated
HAp (cHAp) with structural and chemical similarities to biological apatite. Its
bioresorbable nature was determined by its in vitro solubility under physiological
conditions and was found to be higher than that of HAp.
cHAp nanospheres for tissue engineering scaffolds have been prepared by Zhou
and his group [59] using a nanoemulsion method. Nanoemulsions are a new class of
emulsions having very fine and uniform droplet sizes, usually in the range of
20–200 nm [60]. Using this method, microemulsion-like dispersions can be
obtained using very low surfactant concentrations, or even without any surfactant.
Using this method, nanosized, B-type cHAp particles of spherical shape have been
synthesized [59].
Landi et al. [61] have synthesized Mg-doped HAp by a wet-chemical method
and 5.7 mol% Mg-doped HAp showed the best result in biological applications. No
genotoxicity, carcinogenicity, or cytotoxicity was observed using these materials,
which makes them biocompatible. Mg-doped HAp also showed superior material
resorption and better osteoconductivity than stoichiometric HAp.
HAp has excellent biocompatibility, osseointegration, and biostability [9, 10].
Additionally, its unique characteristic of osteoconduction [11–14] in host osseous
materials has been employed in dental implants [62–66] and in bone cement
applications [67–69]. HAp-based implants are made both from natural products
like animal bones or corals, and also from synthetic HAp. The use of HAp
materials made from animal bones are advantageous because they inherit some
properties such as chemical composition and structure from the raw material
[70–72]. In spite of these advantages, HAp-based implants from synthetic HAp
are preferable because of their uniform composition, high biocompatibility,
overall safety, and their completely controllable microstructure [73]. The
limitations of an HAp implant include its hardness and brittleness, which
makes it difficult to shape in the complex forms required for bone treatment,
and its easy migratory tendency from the implanted sites. To overcome these
limitations, many efforts have been made towards development of novel HAp/
organic polymer composites [74]. In the early 1980s, Bonfield introduced the
concept of using bioactive HAp particles/modified polymer composites as
implant materials for bone replacement [75]. Since then, HAp-modified
polymer-based biocomposites have been widely studied for bone tissue replacement. In the next section, we discuss the use of polymers and give a brief
introduction to these polymers and different methods for their preparation.
148
A. Bhowmick et al.