306
Y. Sasikumar et al.
was about 4 and 13 times lower than the 2 min coated and polished samples. The
polygonal shape MG63 cell adhesion was observed on 13 min coated Ti sample after
2 h culture, and cell proliferation was also increased in 1 and 3 days. Moreover, the
MG63 cell adhesion and its osteogenic differentiation results have shown that the
13 min coated samples promoted osteogenic differentiation. The extracellular matrix
proteins, particularly its early-stage BMP2 expression, were higher on the 13 min
coated alloy, attributed to the tight cell adhesion and pile-up, therefore enhancing
the osteoblast differentiation the micro/nano morphologies produced from MAO
process. Anodized porous titania amorphous tricalcium phosphate (ATP) coatings
incorporating Ca (calcium) and K (potassium) were developed on to Cp-Ti of grade
4 implants from phosphoric acid aqueous solution. Coatings with pore size of about
0.3 µm and the spacing of ~ 1 µm were achieved, and the homogeneous distribution
of Ca and K metal cations with P in the coating was noticed [17]. The Mg, Ca,
and P incorporated Ta 2 O 5 porous nanostructures were developed on to high purity
tantalum sheet using reverse polarization and anodic oxidation process [18]. In the
anodization process (Ta anode), the (ATP: Ca 3 (PO 4 ) 2 ) was deposited on the surface,
while in the reverse polarization approach (Ta cathode), the incorporation of Ca
2+ ,
Mg
2+ , and Na
+ ions was achieved. The increase of surface hydrophilicity and its
roughness suggested its candidature for the biomineralization process.
2.2 Spinal Orthopaedic Implants
The antibacterial activity of the implant is an important criterion to control the formation of biofilm over the implant’s surface. The bacterial infection was the main reason
and limitation of the failure of the implant. Therefore, the surface coatings having
antibacterial properties are developed over the implant surface by incorporating the
antibacterial agents. In a recent study, pure Ti was coated with TiO 2 containing
Ag nanoparticles through the MAO process. The coating consists of microporous
morphology, and Ag was characterized with nanoparticles in the cluster form, and
few stand-alone nanoparticles were also observed in the TiO 2 matrix [19]. Furthermore, doping of Ag nanoparticles will not affect a crystalline phase of TiO 2 and the
wettability of the coated surface was increased (~ 20°) and only minor influence of
Ag doping on the wettability was reported. It was found that the S.aureus and E.coli
bacteria adhesion were controlled, and the amount of Ag will also influence antibacterial activity studies. The samples with higher Ag contents (0.5 and 1.0 g/l) showed
a complete reduction of E.coli and reduction of 6-log S.aureus. The enhancement
in the antibacterial activity was due to the contact of Ag with the bacteria, and the
release of Ag
+ ions could damage the membrane and lead to cell death. Nano-Ceria
coatings with different shapes (rod, cube, and octahedron) developed on the titanium
surface showed variation in the Streptococcus sanguinis adhesion anti-inflammatory
response [20]. The antibacterial and anti-inflammatory effects were better for the
nanooctahedron and nanocubes of CeO 2 coated Ti compared to the nanorod CeO 2
Y. Sasikumar et al.
was about 4 and 13 times lower than the 2 min coated and polished samples. The
polygonal shape MG63 cell adhesion was observed on 13 min coated Ti sample after
2 h culture, and cell proliferation was also increased in 1 and 3 days. Moreover, the
MG63 cell adhesion and its osteogenic differentiation results have shown that the
13 min coated samples promoted osteogenic differentiation. The extracellular matrix
proteins, particularly its early-stage BMP2 expression, were higher on the 13 min
coated alloy, attributed to the tight cell adhesion and pile-up, therefore enhancing
the osteoblast differentiation the micro/nano morphologies produced from MAO
process. Anodized porous titania amorphous tricalcium phosphate (ATP) coatings
incorporating Ca (calcium) and K (potassium) were developed on to Cp-Ti of grade
4 implants from phosphoric acid aqueous solution. Coatings with pore size of about
0.3 µm and the spacing of ~ 1 µm were achieved, and the homogeneous distribution
of Ca and K metal cations with P in the coating was noticed [17]. The Mg, Ca,
and P incorporated Ta 2 O 5 porous nanostructures were developed on to high purity
tantalum sheet using reverse polarization and anodic oxidation process [18]. In the
anodization process (Ta anode), the (ATP: Ca 3 (PO 4 ) 2 ) was deposited on the surface,
while in the reverse polarization approach (Ta cathode), the incorporation of Ca
2+ ,
Mg
2+ , and Na
+ ions was achieved. The increase of surface hydrophilicity and its
roughness suggested its candidature for the biomineralization process.
2.2 Spinal Orthopaedic Implants
The antibacterial activity of the implant is an important criterion to control the formation of biofilm over the implant’s surface. The bacterial infection was the main reason
and limitation of the failure of the implant. Therefore, the surface coatings having
antibacterial properties are developed over the implant surface by incorporating the
antibacterial agents. In a recent study, pure Ti was coated with TiO 2 containing
Ag nanoparticles through the MAO process. The coating consists of microporous
morphology, and Ag was characterized with nanoparticles in the cluster form, and
few stand-alone nanoparticles were also observed in the TiO 2 matrix [19]. Furthermore, doping of Ag nanoparticles will not affect a crystalline phase of TiO 2 and the
wettability of the coated surface was increased (~ 20°) and only minor influence of
Ag doping on the wettability was reported. It was found that the S.aureus and E.coli
bacteria adhesion were controlled, and the amount of Ag will also influence antibacterial activity studies. The samples with higher Ag contents (0.5 and 1.0 g/l) showed
a complete reduction of E.coli and reduction of 6-log S.aureus. The enhancement
in the antibacterial activity was due to the contact of Ag with the bacteria, and the
release of Ag
+ ions could damage the membrane and lead to cell death. Nano-Ceria
coatings with different shapes (rod, cube, and octahedron) developed on the titanium
surface showed variation in the Streptococcus sanguinis adhesion anti-inflammatory
response [20]. The antibacterial and anti-inflammatory effects were better for the
nanooctahedron and nanocubes of CeO 2 coated Ti compared to the nanorod CeO 2