RETRACTED: Nurse’s A-Phase–Silicocarnotite Ceramic–Bone Tissue Interaction in a Rabbit Tibia Defect Model

Abstract

Calcium phosphate materials are widely used as bone substitutes due to their bioactive and biodegradable properties. Also, the presence of silicon in their composition seems to improve the bioactivity of the implant and promote bone tissue repair. The aim of this study was to develop a novel ceramic scaffold by partial solid-state sintering method with a composition lying in the field of the Nurse’s A-phase–silicocarnotite, in the tricalcium phosphate–dicalcium silicate (TCP–C₂S) binary system. Also, we evaluated its osteogenic and osteoconductive properties after being implanted into tibia defects in New Zealand rabbits. X-ray, microcomputer tomography, and histomorphometry studies demonstrated that this porous ceramic is highly biocompatible and it has excellent osteointegration. The material was being progressively reabsorbed throughout the study and there was no unspecified local or systemic inflammatory response observed. These results suggest that ceramic imitates the physicochemical characteristics of bone substitutes used in bone reconstruction.

1. Introduction

Demand for biomedical biomaterials used for restoring bone loss as a result of multiple causes, such as bone diseases (infections, dysplasias, tumors) and traumas, is growing exponentially [1,2]. Nowadays, there is a wide range of synthetic materials that are marketed for this purpose, including synthetic polymers, ceramics, and metals [3,4]. However, their ability to repair bone tissue is not comparable to the effectiveness of the use of autologous cancellous bone grafts and allogenic bone grafts [5]. Nevertheless, these bone grafts present other potential disadvantages like the morbidity, bleeding, limited amount of autologous bone available, and the immunogenic response and insufficient osteogenic ability attributed to allogenic bone grafts [6,7]. For these reasons, several types of synthetic bone graft substitutes are still being developed to replace the use of natural bone grafts. The characteristics of the biomaterials used in regenerative medicine have been evolving over the years, varying their properties and the way they interact with the host tissue. “Third-generation biomaterials” include bioceramics with improved osteogenic properties [8]. Bioceramics belonging to the dicalcium silicate (Ca₂SiO₄)–tricalcium phosphate (Ca₃(PO₄)₂) phase diagram and its subsystems [9,10,11] are good candidates as bone substitutes due to their biodegration/resorption properties, providing adequate levels of silicon (Si), calcium (Ca), and phosphate (P) ions into the biological environment. It has been demonstrated that CaP ceramics can promote osteogenic cellular activities, mineral deposition, and bone formation [12,13]. Also, Si can be released from the ceramics under in vitro [14,15] and in vivo conditions [16,17], and it has unique properties when it is included in CaP ceramics. Silicon is a relevant element in the skeletogenesis process by stimulating the proliferation and osteoblastic differentiation of bone progenitor cells of mesenchymal origin located in the bone tissue [18,19,20]. Furthermore, the resorption capacity of CaP ceramics through a “creeping-substitution” mechanism provides optimal properties as a temporary support to initiate the process of bone colonization by osteoblastic lineage cells and the elements of the hematopoietic bone marrow and blood capillaries located in the host, which are the starting point of the process of bone neoformation.

Accordingly, materials that contain silicon, calcium, and phosphorus are excellent candidates for preparing biomaterials with improved osteogenic properties. The synthesis of Nurse’s A-phase (7CaOP₂O₅2SiO₂) and silicocarnotite (5CaOP₂O₅SiO₂) as monophasic materials was addressed by the present authors in a previous work [21,22,23].On the basis of the Nurse’s A-phase–silicocarnotite in the system Ca₃(PO₄)₂–Ca₂SiO₄, an invariant eutectoid point at 1366 °C ± 4 °C for a composition of 28.39 wt% Nurse’s A-phase–71.61 wt% silicocarnotite was also established [11] and results of proliferation, growth, and osteoblastic differentiation of adult human mesenchymal stem cells on the material proved that the biphasic dense ceramic developed is not cytotoxic [24,25].

Consequently, in this study we have focused our attention on the development of a new biphasic porous Nurse’s A-phase–silicocarnotite by partial solid-state sintering method, which we estimate delivers a good supply of Si, Ca, and P ions. Moreover, we have analyzed its properties of resorption and promotion of the formation of bone tissue in vivo after implanting the bioceramic into bone defects in New Zealand rabbits (Figure 1)

2. Experimental Section

2.1. Preparation of Scaffolds

The starting materials, Nurse’s A (7CaOP₂O₅2SiO₂, A from now on) and silicocarnotite (5CaOP₂O₅SiO₂, S from now on) ceramics, were previously synthesized by partial solid-state sintering method following the process described in previous works [21,23]. A mixture of 71.61 wt% S–8.39 wt% A was prepared. Firstly, S and A bars were ground to powders and the desired proportions of each component were weighed on an analytical balance and were closely mixed in an attrition mill for 1 h using isopropyl alcohol as a grinding medium and yttrium partially stabilized zirconia balls of 1 mm diameter. The resulting mixture was dried at 60 °C overnight. After drying, samples were isostatically pressed in bars at 200 MPa. The bars were placed into platinum crucibles and heated to 1300 °C and maintained for 24 h before being slow-cooled to room temperature at a rate of 6 °C/min. One part of the obtained biphasic material was ground in a tungsten carbide mill to particle size of 1–2 mm, and the other part was milled in a planetary grinding mill to a mean particle size of 2 µm as measured by laser scattering (Master Sizer S; Malvern Instruments Ltd., Worcestershire, UK). Scaffold implants were prepared with 10% 2 µm powder with 90% coarse fraction powder of 1–2 mm, adding 10% polyvinyl acetate (PVA) as a binder [26]. The biomaterial was then heated to 1170 °C and maintained for 2 h, and after that, the biomaterial was allowed to cool inside of the furnace for 24 h. Next, some scaffolds were cut into cylinders (5 ± 0.2 mm diameter and 3 ± 0.3 mm height) in thickness for in vivo tests.

2.2. Characterization of Scaffolds

The obtained scaffolds were conducted to powder and the scaffold’s crystalline phases were determined by powder X-ray diffraction (XRD-Bruker-AXS D8Advance, Bruker, Massachusetts, USA) patterns during continuous scanning from 20 (2θ) to 50 (2θ) with a step size of 0.02° at a scanning rate of 10° min⁻¹. The diffractograms of samples were compared with the database provided by the Joint Committee on Powered Diffraction Standards (JCPDS) database. Fourier transform infrared spectrometry (FTIR-Thermo SCIENTIFIC Nicolet iS5 equipped with an iD5 ATR Accessory) was used to get information of the major functional groups of the scaffolds. Data were collected between 4000 and 550 cm⁻¹ at 20 °C and 64 scans of resolution. The microstructure of the obtained scaffolds was studied by scanning electron microscope fitted with energy-dispersive X-ray spectroscopy (SEM-EDX, SEM-Hitachi S-3500N and INCA system, by Oxford Instruments Analytical, UK, respectively). Samples were covered with palladium according to previous literature protocol [27].

2.3. Surgical Procedure and Implantation

A total of 16 adult male New Zealand rabbits weighing between 4 and 4.5 kg and approximately aged 28–30 weeks old (bone mature, i.e., physis or growth plate closed) were used for this study, approved by the local ethics committee (University of Murcia) in accordance with meeting Spanish and European (BOE 223/1988 and 265/1990) (86/609/CEE) standards for the protection of experimental animals. Four animals (n = 4) were randomly distributed and housed individually for each study period defined (1, 3, 5, and 7 months). After the acclimatization period, in all animals, surgery was performed on both tibias under strict aseptic conditions and general anesthesia following our established protocol [28]. Circular defects (5 mm Ø) were created in the proximal tibial metaphysis and ceramics were implanted. The implants were press fit in the defects to ensure stability. Bone defects on the contralateral tibias were used as blank control (ungrafted). All the animals survived after the surgery. At the end of each time point of the study, animals were sacrificed with an overdose of a lethal injection of sodium pentobarbital (50 mg kg⁻¹) Dolethal^® (Lab. Vetoquinal. Lure Cedex. France) given intracardially after deep sedation (Ketamine, 0.5 mg k⁻¹, im, single dose). After that, the tibias were collected and stripped of adhering soft tissues, then were fixed in 4% paraformaldehyde and stored at 4 °C for one week until further examinations.

2.4. Conventional Radiological Study

X-ray radiographies (lateral view) of both tibias at different time points were taken to assess implant evolution and bone response. Initial bone X-rays were performed with 32 kV, 40 mA, DFO 40 cm, fine focus, automatic exposimetry without antiscatter grid but using GAP effect to get magnified images. Subsequently, Elite Kodak photographic film images were obtained for slides (Kodak^® Madrid, Spain) and digitized with an Epson film-scan 2000 (Epson^®, Madrid, Spain) that facilitated their study in BMP and JPG formats.

2.5. Micro-CT Evaluation

The tibia specimens were imaged with micro-CT (mCT) scanning in order to quantify the new bone formation and reabsorption of scaffolds in bone defects. The bone samples were scanned using a high-resolution mCT (Skyscan 1172^®, Bruker microCT NV, Kontig, Belgium). The X-ray source was fixed at 80 kV and 124 µA, with a pixel size of 12 µm and using a 1 mm aluminum filter. The tibial sample was set on the object stage and the scanning was performed over a 360° rotation with images acquired every 0.4°. After scanning, the images were reconstructed based on the Feldkamp algorithm (Feldkamp et al., 1984) (Donath and Breuner, 1982), using the NRcon software (Bruker microCT NV, Kontig, Belgium). The reconstructed images were evaluated using Data Viewer software (Bruker microCT NV, Kontig, Belgium) and positioned to ensure that the implanted biomaterial was viewed with its cylindrical shape for performing data analysis. To define the volume of interest (VOI), the biomaterial limits were selected, avoiding all the tissue outside the implanted material. Finally, an analysis of the material properties and porosity was performed using the advanced porosity method note described by Bruker and an analysis of the bone quality using standard indices for the determination of the cancellous bone microstructure (Hildebrand et al., 1999). In order to quantify the bone morphometry and structural properties of biomaterial, the following parameters were studied: bone volume (BV_b) and ceramic volume (BV_c-mm³), ratio of bone volume (BV_b/TV) and ratio of ceramic volume (BV_c/TV) with respect to total volume studied (VOI-%), Po. N (cl) as number of closed pores (i.e., those surrounded in all directions of the 3D structure by material), Po. V (cl) as volume of the VOI occupied by closed pores, Po. S (cl) as VOI surface occupied by closed pores, Po. (cl) as percentage of the VOI occupied by closed pores, Po. N (op) as number of open pores (i.e., those spaces surrounded by material but not in all directions), Po. V (op) as volume of the VOI occupied by open pores, Po (op) as percentage of the VOI occupied by open pores, Po. V (tot) as total volume of the VOI occupied by open and closed pores, Po (tot) as percentage of the VOI occupied by open and closed pores, and Eu. N (Euler number) as an indicator of the connectivity of a complex three-dimensional structure. [29,30].

2.6. Histological and Histomorphometric Study

For histological preparation, tibia regions where implants and control defects were located were cut in blocks or segments of bone (0.5 cm in length) using an oscillating saw, fixed in 4% formaldehyde in 0.1 M phosphate buffer (pH 7.2), and identified. Then, the blocks were washed in PBS, dehydrated in different graded ethanol series (70%, 96%, 100%), and infiltrated with different graded mixtures of ethanol and glycometacrylate (30:70, 50:50, 70:30, and 100%) (Technovit 7200 VLC, Heraus Kulzer, Werheim, Germany) following guidelines previously published [31]. The samples were then polymerized and heated at 37 °C for 24 h to ensure a complete polymerization. Serial cross-sections of 200 μm thickness perpendicular to the longitudinal axis of the tibia, where the material or control defect was placed, were done using a band saw and mechanically micropolished (Exakt Apparatebau, Norderstedt, Germany) using 1200- and 4000-grit silicon carbide papers (Struers, Copenhagen, Denmark) until samples were obtained with a thickness of approximately 40 μm. The slides were stained using the Levai–Laczkó method and Masson trichrome staining for both histologic and histometric analysis. For histomorphometric examination, three samples per tibia were studied. Five fields per section obtained from the middle of the implanted area and control bone defect ungrafted were observed. A quantitative analysis was performed of: (a) the proportion of the area occupied by newly formed bone, both around and inside the material, (b) the implanted material (residual graft materials), and (c) the structure of the cortical bone defect in terms of surface area and volume to determine defect closure. Image analysis was conducted based on the color and shape of these structures, differentiating the new laminar bone from connective and vascular tissue (Adobe Photoshop^®, CA, USA). Parameters were evaluated and measured using the image analysis program Cell-sens 1.5^® (Olympus Corporation, Japan).

2.7. Statistical Analysis

Data were statistically analyzed using SPSS for windows (SPSS Inc., Chicago, IL, USA) by means of the Student’s paired t-test and Friedman’s test for nonparametric samples in median comparison. Results were considered statistically significant at p-values < 0.05.

3. Results

3.1. Scaffold Characterization

By the partial solid-state sintering method, it was possible to produce highly porous biphasic scaffolds. SEM observations revealed pore diameters that ranged from 200 µm to 1.0 mm, and a pore wall thickness of ~50 µm (Figure 2a). Micropores from 1 μm to 10 µm were also viewed on pore walls and struts (Figure 2b). The scaffold composition, determined by a quantitative analysis by EDS at different sample points, was around 15.1 wt% SiO₂, 58.2 wt% CaO, and 26.6 wt% P₂O₅, close to the composition of the synthetized material determined by chemical analysis. The XRD pattern of the biphasic scaffold is also shown in Figure 2c. No new phase (after sintering) was formed and all peaks corresponded solely to S and A, according to the Joint Committee on Powered Diffraction Standards (JCPDS). The FTIR spectrum of the sintered A–S scaffold was obtained, presenting the characteristic peaks (Figure 2d). Typical bands originated by SiO₂ and PO₄ ²⁻ groups were present. The scaffold exhibited intensive IR bands in the 550–1050 cm⁻¹ spectral region divided in two IR band groups: the first one between 550 and 650 cm⁻¹ and the second one in the 840–1050 cm⁻¹ spectral region. At wavelengths lower than 900 cm⁻¹, the absorption bands were related with those corresponding to the silicate network, mainly to the symmetric stretching mode of SiO₄ groups. The bands observed from 840 up to 1000 cm⁻¹ correspond to the overlapping of stretching vibrations of phosphate and silicate groups [32,33,34]. Over 1000 cm^-1 absorption bands can be mainly related with the phosphate group. Finally, in the region between 1100 to 1400 cm⁻¹, no well-defined adsorption bands were observed.

3.2. Conventional Radiological Study

Figure 3 shows the lateral X-ray view of the bone section that contained the implant from one to seven months implantation as well as the control. The control defect (ungrafted) (Figure 2, top) corresponded to a well-defined area of lower radiological density that returns to normal characteristics disappearing one month after surgery, without causing heterotrophic ossification or irregularities in the external limits of the bone. The implanted material is a cylindrical ceramic easily visible inside the bone due to its greater radiological density and granulated appearance (Figure 2, bottom). One month after surgery, the bone defect created for the implantation of the ceramic was apparently closed, but cortical bone showed low radiological density in that area. After three months of implantation, cortical bone where the defect was created continued showing lower radiologic density, although the ceramic showed a decrease in its radiological density and presented a more irregular contour. As the study time progressed, the cortical bone recovered completely after five months of implantation, showing a radiological density similar to the adjacent normal areas. At the end of the study (seven months), the implant showed a generalized decrease in its radiological density, presenting an oval shape and irregular edges poorly defined, as well as an increase of radiolucent areas in its interior that could indicate zones of resorption of the implant. In addition, some trabeculae of the adjacent bone tissue seemed to be introduced and incorporated into the implant interior. In this last period, the implant was still seen in the metaphyseal area, which demonstrated the absence of complete resorption or its replacement by newly formed bone.

3.3. Micro-CT Evaluation

In general, 2D and 3D images (Figure 4a,b, respectively) showed that implant volume and surface were reduced thorough the study period. After three months of implantation, irregularities in the ceramic surface started to appear, increasing the number and the size of open pores. At the end of the study, fragments of implant remained in the metaphysis of the tibias. At the same time, new bone formed inside the bone defect artificially created was increased in all periods of the study (Figure 4c). Analysis of the 3D images showed that bone volume (BV, bone volume/mm³) was significantly increased inside the bone defect studied (VOI) while ceramic volume was decreasing (p < 0.05). The porosity analysis showed that the volume of open pores increased significantly during the study (p < 0.05) (Figure 3d), while the closed pores decreased significantly (p < 0.05) (Figure 4e). In addition, a significant increase in the Euler number related to the increase in porous connectivity was determined (p < 0.05) (Figure 4f).

3.4. Histological Analysis

The histological sections of the scaffold were analyzed at 1, 3, 5, and 7 months after the implantation and stained with the Levai–Laczkó method and Masson trichrome. As shown in Figure 5, histologic evaluation of control defects showed that the defect was not repaired (yellow arrow) one month after surgery, and no inflammatory sign was seen. After three and five months, control defects were fully occupied by new trabecular bone tissue with normal appearance. In the last stage of study, control defects were completely repaired by a structurally well-organized mature compact bone tissue.

One month after the implantation of ceramics into tibias (Figure 6a–d), thin trabeculae of neoformed bone with normal characteristics were observed surrounding the entire periphery in direct contact with the material surface without interposition of fibrous tissue. Incipient granulation tissue composed of fibroblasts, blood capillaries, and isolated and disorganized fibers with the appearance of collagen was visible inside the material from the earliest point of the study. Nonspecific inflammatory infiltration mediated by inflammatory cells (granulocytes/neutrophils, monocytes/macrophages, lymphocytes) was not observed at this time. At three months (Figure 6e–h), ceramic architecture was conserved, but there were some areas of resorption inside the ceramic compared to the previous period, and pores increased their diameter, facilitating the colonization of the material by repair tissue. Thereby, the presence of some nonmineralized bone matrix (osteoid) in the granulation tissue was seen arranged both inside and surrounding the implanted material. Porosity was increased after five months of implantation (Figure 6i–l) due to the progressive increase of material resorption. The cortical defect was totally recovered and repaired by normal compact bone tissue, which continued with bone trabeculae that were surrounding the ceramic and establishing a reticular net that occupied all the extension of the implant. Figure 6m–p shows the material status at the end of the study (seven months). The material was irregularly fragmented and dispersed inside the bone medullary cavity. In some areas, the new bone tissue was similar to a mature well-organized compact bone, distinguishing mineralized extracellular matrix arranged in bone lamellae, which can be organized concentrically around a Havers’ channel (compact osteon-type bone) interconnected by Wolkman channels.

3.5. Histomorphometric Study

In this study, new bone tissue formation (Figure 7a) was higher in tibias after implantation of bioceramics than in control tibias in all study periods. The cortical bone located in the bone defect created for the implantation (defect closure) (Figure 7b) was gradually increased. The bone defect where ceramics were implanted reached a linear closure of 93% at the end of the study. In the control defect, the cortical bone was also increased, but it was significantly lower than in the implant defect (p-value < 0.05). Furthermore, the implant was progressively reduced (Figure 7c) throughout the study period, reaching 16.69 ± 2.16% in the last period (seven months), which meant an overall reduction of 83% approximately.

4. Discussion

Nurse’s A-phase–silicocarnotite porous scaffolds, obtained by partial solid-state sintering, were processed to be used as a novel resorbable porous material with osteoconductive properties for the reconstruction of bone losses or bone defects. The results showed that the porous scaffolds were degraded and removed from the place of implantation throughout the experimental set points and allowed new bone tissue formation to occupy this site. In this study, the results after the intraosseous implantation of the material did not show the existence of any nonspecific inflammatory response, or evidence for tissue necrosis and the absence of a layer of fibrous tissue interposed between the surface of the material and the neoformed osseous tissue, indicating that this bioceramic is well tolerated by the recipient organism (biocompatible). In the ceramic–bone interface, an initial fibroblastic proliferation was produced as part of the repair tissue (granulation tissue), which was later replaced by trabecular bone tissue with normal histological characteristics. In addition, we did not see in any of the histological sections the presence of fibrotic tissue between the ceramic and the host bone. On the other hand, radiological studies showed that the material does not cause local changes such as areas of osteolysis around the material, which might suggest the interposition of soft tissues isolating the material from the receptor tissue or bone rarefaction zones indicating suspicion of local infection. In our concrete case, the radiological characteristics of the adjacent bone were the same as those observed in the control group. In this way, all these results confirm the osseointegration capacity of this material, probably due to morphological characteristics and because these materials are composed of Ca and P, the main ion components of hard tissues [35]. Also, the ions released to the host tissue were probably able to be incorporated without any trouble by different metabolic pathways [36]. Osteoconductivity is, conceptually, the ability to guide the bone growth within a porous scaffold, and this item was also evaluated. Histological and radiological studies showed that the newly formed bone gradually grew centripetal inside the porous scaffold since the first month after the implantation of the biomaterial. One of the most important factors that promote osteoconductivity is the porosity, referring to the pore size, the interconnection between pores, and the total pore volume of the material with respect to the volume of the sample [37]. Furthermore, it has been shown that microporosity plays an important role in the process of bioreabsorption of the material, facilitating the infiltration of the material by fibrovascular tissue, as well as its revascularization, allowing bone regeneration [38]. In this case, SEM observations revealed pore diameters that ranged from 200 µm to 1.0 mm. Therefore, this is a highly reabsorbable bioceramic that favors the osteoconductivity of the material thanks to macroporosity [39,40]. Micropores from 1 μm to 10 µm were also viewed. Despite the fact that some researchers have indicated that bone growth is quite difficult in ceramics with pores smaller than 100 µm [41], we could observe in anatomopathological assays that this bioceramic had many interconnections between the pores that led to bone growth inside it. Furthermore, micro-CT analysis permitted us to check the existence of open pores (35%) that were incremented thorough the study until reaching 68%, and the increase of connectivity (Euler number from −686 to −116 at the end of the assay), agreeing with some researchers that think that interpores favor the bone growth inside them [42]. Micro-CT and histomorphometric analysis allow us to quantify objectively bone formation, among other parameters. In our experiment, we could see that new bone formation was higher in the implant group (20%) than in the control group (7%) by the end of the study period. Also, cortical closure was faster and with more bone quantity (93% implant group, 67% control group). Furthermore, we counted histomorphometrically that the contact area between implant and new bone formed increased from 36% the first month to 58% at seven months. The usually recommended pore size is between 100 and 400 µm [40,41,42]. Our results agree with some authors that observed better results in materials with a pore size of 50–100 µm than of 200–400 µm [43], even though other researchers described that the right pore size for bone grafts should be between 210 and 300 µm [44] or higher [45]. At this point, it is difficult to correctly interpret the results of the published studies, due to the great variability in relation to the physical and chemical properties of the materials used in each one, being not very specific and even unknown sometimes, so the results between the different studies cannot be comparable using porosity as the only parameter of study. Referring to the biodegradation of Nurse’s A-phase–silicocarnotite bioceramic, material quantity was clearly decreased during the assay, but it remained until the end of the study period (16% of initial volume). Since the first month after the implantation, we observed a change in histological color of the material, from black to grey in some areas, and a loss of radiological density that could be related to a passive chemical dissolution. This observation is based on the fact that when these kinds of materials are immersed in phosphate buffered solution (pH 7.4) or deionized water, their dynamic surface leads to a liberation of Ca, P, and Si ions [20,27], which contribute to a high radiological density. This step could be the origin of the formation of small fragments, which could be small enough to be phagocyted by macrophages, starting the reabsorption process. This was revealed with the appearance of lacunae or resorption areas on the surface of the material, besides the presence of multinucleated cells with macrophagic or osteoclastic aspects, in whose interior were observed some particles of material (images not shown). Highly biodegradable materials are good candidates for bone substitution, since they are also capable of releasing ions. In our specific case, the role of Si is decisive, supporting cell proliferation and the synthesis of collagen by osteoblasts [18]. Numerous studies have shown that α-TCP has a high rate of resorption [46,47], despite the fact that the resorption rate is lower than ß-TCP [48]. However, balance between the rate of material degradation and the new bone growth is crucial, since an excessively high reabsorption rate of the material can be related with an excess resorption of the newly formed bone [49]. Also, it has been shown that the rate of dissolution of αTCP decreases when Si ions are incorporated into the structure of the ceramic, achieving a more progressive and appropriate bone turnover [18,50]. In our study, the material had partially degraded without being fully reabsorbed. This reabsorption occurs in parallel with an increase in newly formed bone, a phenomenon known as “creeping substitution” [50,51], which considers that the incorporation of the material into the bone is favored by its fragmentation, being continuously replaced by the newly formed bone. In previous studies [52], we determined that the increase of C₂S proportion in TCP-C₂S ceramic tends to decrease the resorption time of the material. On the other hand, an increase in the proportion of C₂S leads to a major bone tissue formation, probably due to the Si released to the surrounding tissue. In this case, although SiO₂ is around 15% of the total weight of this bioceramic, we observed that new bone formation is slow, and it would probably be necessary to increase the Si ion content of the material to contribute to a major new bone formation.

5. Conclusions

In this study, the Nurse’s A-phase–silicocarnotite scaffold has demonstrated that it is a bioactive, biocompatible, and biodegradable ceramic. In addition, it has proven to be a highly osteoconductive biomaterial, allowing the rapid formation of a granulation tissue which later was replaced by trabecular bone tissue and compact bone (compact osteon-type bone), both at the periphery of the implant and inside it. Therefore, it could be considered as a potential bone substitute to be used in a variety of medical applications such as bone defects filling and implant covering in orthopaedic surgery and traumatology, oral and maxillofacial surgery, and neurosurgery.