Bioactive glasses (BAG), first melt-derived in the late 1960s by Larry Hench, obtained good clinical results in dentistry, due to their properties of good bioactivity, when used to treat bone defects [1]. The composition of this bioactive glass was 45 wt% SiO 2 , 24.5 wt% Na 2 O, 24.5 wt% CaO, and 6 wt% P 2 O 5 , which was later termed as 45S5 or Bioglass®. Recently, various researchers have incorporated BAG into experimental[2-5] and commercial dental resin composite materials [6]. The release of calcium and phosphate ions was used as a means to assist with prevention of demineralization of dentine from an initial caries attack. Furthermore, BAG-containing resin compos-ites can reduce bacterial penetration into marginal gaps due to their ability to increase local pH, precipitate apatite on the surface, or in this case within the gap [7]. In addition, a novel design of resin composite-based implant containing bioactive glass has successfully been used for many years [8,9]. The fiber-reinforced composite implants loaded with bioactive glass were supported to enhance biological bone repair and the formation of vascularized structures, in addition to providing improved antimicrobial properties for implants. Chemically speaking, this type of "bioactive" action is a mineralization reaction. At the beginning, a silica-rich layer with Si-OH groups forms on the surface by the exchange of Na + and Ca 2+ ions from the glass with surrounding H + ions, which increases surrounding pH. Then, Ca 2+ and PO 3 4− from surrounding solution forms amorphous calcium phosphate (ACP, Ca x (PO 4 ) y •nH 2 O)[10] on the surface, which is transformed into octacalcium phosphate (OCP, Ca 8 (HPO 4 ) 2 (PO 4 ) 4 •5H 2 O) [10] and finally evolves into nanocrystalline carbonated hydroxyapatite (CHA, Ca 10−x (PO 4 ) 6−x (CO 3 ) x (OH) 2−x−2y (CO 3 ) y ) not hydroxyapatite (HA, Ca 10 (PO 4 ) 6 (OH) 2 ) in human body as bone or tooth enamel [11,12].