Enhancement of Bone Tissue Repair by Octacalcium Phosphate Crystallizing into Hydroxyapatite In Situ
OCP enhances differentiation of osteoblastic cells in two- and three-dimensional conditions.
OCP enhances osteoclast formation from bone marrow cells (macrophages) in the co-culture with osteoblasts by raising osteoclast-inducing factor (RANKL).
OCP enhances macrophages migration.
These cellular responses are brought about associated with the hydrolysis of OCP toward a nonstoichiometric Ca-deficient hydroxyapatite (HA), which is accompanied by physicochemical changes such as inorganic ion exchanges and serum proteins adsorption.
Combining OCP with natural polymers, such as collagen and gelatin, improves not only their moldabilities but also increases the osteoconductivity and the biodegradability in vivo. The hydrolysis of OCP may be involved in displaying bone regenerative capacity of OCP.
KeywordsOctacalcium phosphate (OCP) Hydroxyapatite·Hydrolysis Osteoblasts Osteoclasts Bone substitute materials
It has been advocated that octacalcium phosphate (OCP, Ca8H2(PO4)6 · 5H2O) could be a precursor phase to biological apatite crystals in the bone (Brown 1966) although there is still a controversy about whether OCP is actually present in bone mineralization (Rey et al. 2014). It has been reported that in a highly supersaturated calcium and phosphate solution with respect to hydroxyapatite (HA, Ca10(PO4)6(OH)2), amorphous calcium phosphate (ACP, Ca3(PO4)2 · nH2O) is formed first, and then it transforms to an OCP-like phase before crystallizing to the thermodynamically most stable HA phase (Meyer et al. 1978) at physiological pH. ACP has been confirmed in growing chicken embryonic long bone (Kerschnitzki et al. 2016). The structure of the OCP-like phase has been suggested to resemble HA having a similar characteristics in X-ray diffraction (XRD) (Meyer et al. 1978). In fact, it has been shown that an apatite structure, having a solubility similar to OCP, can be synthesized in the presence of fluoride ions (Shiwaku et al. 2012). It has also been shown that ACP is aggregated as a cluster forms and then transforms to HA via a Ca-deficient OCP-like structure (Habraken et al. 2013) and that growing calcium phosphates involve the common cluster structure throughout the HA formation (Onuma et al. 2017). We hypothesized that the introduction of synthetic OCP into bone defects should lead to the enhancement of the initial deposition of bone matrix followed by additional bone formation (Suzuki et al. 1991). An experiment of onlay graft of OCP in the granule form onto mouse calvaria, in comparison with HA materials, was conducted to test the hypothesis and showed that OCP enhances the appearance of bone tissue around these granules more than those by HA materials (Suzuki et al. 1991). This review article summarizes how the OCP materials work in bone repair if placed in bone defects and in the vicinity of bone-tissue-related cells in vitro.
20.2 Bone-Bonding Property of OCP Implanted in Bone Defects
It has been proposed that direct bone bonding of ceramic materials is brought about through an apatite layer formation on the materials, thereby allowing chemical bonding between newly formed bone apatite crystals and the apatite formed on the materials (Kokubo 1991). Such direct bonding has been reported to occur in ceramic materials, such as glass ceramics (Hench et al. 1973; Kokubo 1991), HA (Aoki 1973), and β-tricalcium phosphate (β-TCP, Ca3(PO4)2) (Kotani et al. 1991). The property is ascribed to the osteoconduction, which is defined as the bone formation taking place in orthotopic site (LeGeros 2002). We have found that when the tissue response was observed using undecalcified sections of the granules of OCP implantation onto mouse calvaria by transmission electron microscopy, newly formed bone crystals directly bonded to the surface of crystals in the OCP granules (Suzuki et al. 2008). From this observation, it was apparent that the OCP has an osteoconductive property (Oyane et al. 2012).
20.3 Hydrolysis from OCP to Ca-Deficient HA in Physiological Conditions
It is known that OCP is more soluble than β-TCP and HA and less soluble than dicalcium phosphate dihydrate (DCPD, CaHPO4・2H2O) under neutral pH (Brown et al. 1981; Chow 2009). It is of interest to learn about whether OCP is actually converted to HA in vivo conditions. It has been expected that OCP is converted (hydrolyzed) to HA if placed in the in vivo environment (Suzuki et al. 1991). There is a general consensus that OCP is stacked by apatite layer alternatively with hydrated layers and that the hydrolysis is once initiated; it advances spontaneously and irreversibly (LeGeros et al. 1989; Suzuki et al. 1995a, b; Tomazic et al. 1989). The structural changes of OCP have been investigated because the laboratory synthesized OCP is a well-grown crystal (Kobayashi et al. 2014; Sakai et al. 2016; Suzuki et al. 1991, 2006a, b). Other investigations showed that OCP remained untransformed in simulated body fluid (SBF) even prolonged incubation (Ito et al. 2014) under supersaturated conditions with respect to HA theoretically estimated (Lu et al. 2005). The implantation of OCP in the bone and subcutaneous tissues promoted the structural changes in XRD (Suzuki et al. 1991, 1993, 2006b) and in Fourier transform infrared (FTIR) absorption from that of OCP to apatite structure with increasing Ca/P molar ratio (Sakai et al. 2016) and carbonate ion containment (Suzuki et al. 2009) although characteristics of OCP in XRD still remained (Sakai et al. 2016; Suzuki et al. 1991, 1993, 2006b). One of features in the structural changes of OCP by its implantation and incubation in physiological conditions is that the chemical composition of Ca/P molar ratio has never reached to that of a stoichiometric value (1.67) but tends to go to producing a Ca-deficiency, resulting in the formation of a Ca-deficient HA (Sakai et al. 2016; Suzuki et al. 1995b). OCP hydrolysis can be enhanced with experimentally given higher supersaturated conditions in vitro by promoting calcium ion consumption into the crystals and phosphate ion release from the crystals (Kobayashi et al. 2014; Sakai et al. 2016; Suzuki et al. 2006a), suggesting that in vivo environment could be providing such an ionic conditions. It has been reported that human serum is saturated with respect to OCP (Eidelman et al. 1987), which is not contradict to the proposition that HA can be grown on OCP template (Miake et al. 1993).
20.4 Osteoblastic Cell Response
It was observed that, when the granules of OCP were implanted onto mouse calvaria, the crystals of OCP were accumulated by circulating non-collagenous serum proteins, including α2HS-glycoproteins and apolipoprotein E (Kaneko et al. 2011; Suzuki et al. 1993), the ultrastructure of which bears a close resemblance to the tissue structure so-called bone nodules, which is considered as the initial bone deposition locus in intramembranous bone development (Barradas et al. 2011; Suzuki et al. 1991). Osteoblasts then started to form a collagenous bone matrix around the bone nodule-like OCP-protein complex (Suzuki et al. 1991, 2008), indicating that OCP acts on a nucleus of bone formation. From these observations, it was hypothesized that OCP may activate osteoblastic cell activity on its surfaces. In order to test the hypothesis, mouse bone marrow stromal ST-2 cells were inoculated on OCP particles coated on plastic cell culture plate in comparison with HA materials (Anada et al. 2008; Suzuki et al. 2006b). mRNAs of osteoblast differentiation markers, such as alkaline phosphatase (ALP), type I collagen, and osterix, increased with increasing the dose of OCP (Anada et al. 2008).
20.5 Osteoclastic Cell Response
20.6 Bone Substitute Materials
OCP cannot be sintered with keeping its crystalline phase, unlike HA and β-TCP, due to the inclusion of large amount of water molecules (Brown et al. 1962). The granules or the precipitates of OCP were combined with various natural polymers, such as collagen, gelatin, alginate, and hyaluronic acid, in order to acquire the moldability and improve the handling property (Fuji et al. 2009; Handa et al. 2012; Kamakura et al. 2006; Shiraishi et al. 2010; Suzuki et al. 2014). OCP/collagen was made of OCP granules mixed with re-constituted collagen matrix (Kamakura et al. 2006). OCP/gelatins were made of OCP granules mixed with re-constituted gelatin matrix (Saito et al. 2016) and OCP directly precipitated with gelatin molecules (Handa et al. 2012). OCP/collagen composite enhanced the bone formation more than OCP alone when compared in a rat critical-sized calvaria defect (Kamakura et al. 2006). Bone regeneration was augmented in a dose-dependent manner of OCP in the collagen matrix (Kawai et al. 2009), which corresponded to the tendency of increasing osteoblastic cell differentiation in vitro (Anada et al. 2008). After preclinical trial (Kawai et al. 2014), the OCP/collagen composite is under a company-initiative clinical trial in the field of oral surgery in Japan. The OCP-co-precipitated gelatin composite showed a highly biodegradable property in critical-sized rat calvaria defect (Handa et al. 2012) and also in rabbit tibia defect which is an orthopedic bone defect model (Chiba et al. 2016). The inclusion of OCP crystals in gelatin was shown to produce an oriented bone regarding newly formed collagen matrix (Ishiko-Uzuka et al. 2017). OCP/alginates were made of OCP granules mixed with a calcium-cross-linked re-constituted alginate matrix (Shiraishi et al. 2010) and OCP directly precipitated with alginate molecules (Fuji et al. 2009). The combining OCP with alginate allowed the composite to proliferate osteoblastic cells although the alginate is a material that does not have a cellular binding motif (Fuji et al. 2009). OCP/hyaluronic acids (HyAs) were made of OCP granules mixed with HyA medical products, having different molecular weights (Suzuki et al. 2014). OCP/HyAs acquired injectability and OCP combined with a lower molecular weight HyA and with a higher molecular weight HyA enhanced bone augmentation more than OCP alone when placed on the subperiosteal region of mouse calvaria through an osteoclastic resorption of OCP (Suzuki et al. 2014). Thus, the osteoconductive property and the handling property of OCP could be controlled by those natural polymers that are combined with OCP.
It seems likely that the enhancement of bone formation by OCP implantation is derived from its stimulatory capacity on osteoblastic cell activity during its crystallizing into Ca-deficient HA. OCP-based materials could be used as bone substitute materials in various bone defects.
This study was supported in part by grants-in-aid (17076001, 23106010 17K19740 and 18H02981) from the Ministry of Education, Science, Sports, and Culture of Japan, the Uehara Memorial Foundation, the Suzuken Memorial Foundation, and the Iketani Science and Technology Foundation. The author thanks Emeritus Professor and former President of Japan Fine Ceramics Co. Ltd., S. Ito; Professors R. Kamijo, M. Nakamura, and M. Takami, Showa University; Professor T. Katagiri, Saitama Medical School; Professors E. Itoi, S. Kamakura, T. Takahashi, and Emeritus; Professors M. Sakurai, M. Kagayama, and S. Echigo, Tohoku University; Drs. T. Kawai, and Y. Shiwaku, Tohoku University; and Dr. Y. Honda, Osaka Dental University.
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