composites and \(\alpha\)TCP is the major constituent of the powder component of various hydraulic bone cements [9; 10; 11; 12]. In spite of having the same chemical composition, \(\alpha\)- and \(\beta\)TCP differ considerably in their structure, density and solubility, which in turn determine their biological properties and clinical applications.  
From a biological point of view, \(\alpha\)TCP is non-toxic, osteeconductive and bioactive, both in vitro and in vivo. The main reason for the growing interest in \(\alpha\)TCP as a bone implant material, biodegradability. It is more bioreabsorbable than hydroxyapataie (HA), \(\beta\)TCP and biphasic (HA-BTCP) bioceramics currently used in clinical practice. This makes \(\alpha\)TCP an ideal implant material, which is able to be replaced by new bone faster than the other calcium-phosphate-based materials currently available on the market.  
One of our recent works involved synthesizing a new form of \(\alpha\)TCP doped with a dicalcium silica (C\({}_{2}\)S) bioceramic powders in the silicocarnotite-tricalcium phosphate subsystem [13] and addition, prepared dense \(\alpha\)TCP doped ceramic discs by solid-state processing [14]. One of our \(\alpha\)TCP studies has reported the exceptional carbo-hydroxyapatite mineralization ability of \(\alpha\)TCP doped ceramic discs in simulated body fluids [15; 16]. The released Ca, Si and P, who contained the \(\alpha\)-products from \(\alpha\)-TCP doped ceramic, greatly promoted osteogenic different cation \(\alpha\)-human mesemy, mal stem cells [17; 18]. [PERSON] et al. found that Si-TCP grafts displayed greater \(\alpha\)-mensional stability and better bone to implant contact (BIC) at a % reabsorption rate of \(\alpha\)-T\(\alpha\).5% of \(\alpha\)-T\(\alpha\).42.2% of Si-TCP at day 60 of implantation [19; 20; 21]. What these findings indicate is that the cher \(\alpha\)-TCP bioceramics is key to enhancing the in vivo behavior of TCP implants.  
However, to date, studies on Si-\(\alpha\)TCP bioceramic have worked with ceramic discs; hence, none have reported on the fabrication and properties of the \(\alpha\)-dimensional (3-D) scaffolds. Developing porous Si-\(\alpha\)TCP scaffolds to be used as carriers for both \(\alpha\)-type doping or as specific release vehicles is therefore of much interest.  
Three-dimensional scaffolds for bone its use \(\alpha\)-ring are subject to many interrelated biological and structural requirements which must be take into consideration when selecting the suitable biomaterial for fabrication. An ideal bone tis \(\alpha\)-scaffold should possess an interconnected porous structure; i.e., it should be highly \(\alpha\)-meable, with a porosity of \(>\)90% and pore diameters in the range 10-500 \(\mu\)m for cell seeding (tissue ii) growth and \(\alpha\)-scularization, as well as for nutrient delivery and waste removal [22; 23; 24; 25; 26; 27]. A \(\alpha\)-scium criterion of tissue engineering scaffolds is the mimicry and implementation of the bi-dal porosyny of cancellous bone tissue, which is an important factor for effective sca-sd vasculariza, and for bone ingrowth [28]. Microporosity (\(\approx\)2-10 \(\mu\)m, \(<\)50 \(\mu\)m) is essential f-im, diate protein a-cell adhesion, cell migration and osteointegration [23; 24; 27]. Higher por sizes (\(>\)-mm) are required for enhanced new bone formation, greater bone ingrowth and the formation of ca-rings [22; 23; 25; 29; 30].  
In this study, we apply a polymer replication method [22; 31; 32; 33] to prepare Si-\(\alpha\)-TCP scaffolds a highly controlled macro and micro structure and pore interconnectivity and we investigated how it is more more homology affected their osteeconductivity and resorption process in vivo for the first thin.