Bone regeneration in CSBDs is often limited by factors such as defect size, inadequate vascularization, and the absence of a repair-friendly environment. In this context, ceramic-based scaffolds, such as hydroxyapatite (HA), tricalcium phosphate (TCP), and bioactive glass, emerge as promising solutions. These materials serve as three-dimensional matrices that mimic the natural properties of bone, promoting osteoconduction and supporting bone regeneration. However, significant challenges remain, such as improving the integration between the scaffold and native bone, optimizing porosity to support vascularization, and adapting mechanical properties to meet biomechanical demands [7; 8; 9]. Ceramic-based synthetic bone scaffolds (e.g., HA, TCP [10], bioactive glasses, betatricalcium phosphate [\(\beta\)-TCP], bioactive silicates, and their derivatives [11; 12]) are designed with porous architectures featuring interconnected macro- and microstructures that mimic the mechanical and structural properties of natural bone [10; 13]. This design ensures robust mechanical support during healing, particularly in load-bearing or stress-prone areas. Additionally, these scaffolds can support cell proliferation, migration, and differentiation. Some even act as vehicles for the controlled release of growth factors, further promoting bone regeneration [1; 10; 11; 12; 13; 14; 15; 16; 17]. These scaffolds are highly suitable for maxillofacial bone regeneration due to their exceptional biocompatibility, bioactivity, and structural similarity to natural bone. They mimic the mineral phase of bone, promoting osteoconduction and integration with surrounding tissues. Their porous architecture enables vascularization and cellular infiltration, which are essential for new bone formation and nutrient exchange. Furthermore, ceramic scaffolds can be engineered to degrade at a controlled rate, to align with the body's natural bone healing process [18,19]. Despite lacking osteoinductive and osteogenic properties, the wide variety of ceramic materials with osteoconductive properties offers great potential to advance bone regeneration [11,15,16]. The choice of specific ceramic material depends on the desired properties, such as degradation rate, cell adhesion, and mechanical requirements [2,12,14,15]. The advent of 3D printing and other additive manufacturing (AM) techniques has revolutionized the creation of customized scaffolds tailored to the specific needs of each application. This is particularly relevant in OMS, where anatomical complexity demands personalized solutions that also address important aesthetic requirements, such as reconstruction after oncologic resection. Three-dimensional printing enables the fabrication of scaffolds with complex, controlled geometries, allowing for adjustments to parameters such as porosity and spacing between printing lines [1]. Despite advances, no ideal scaffold material has been identified, and research continues to focus on optimizing the integration between the scaffold and native bone [12,17]. Animal models, especially large animals, are essential for preclinical evaluation, as they serve as a significant analog to the human body, thereby facilitating translational research. These models enable the assessment of critical scaffold properties, including pore size and interconnectivity, as well as mechanical strength, and facilitate the analysis of osseointegration processes [20]. Although many studies have investigated ceramic-based scaffolds for bone regeneration, there is no consensus on the optimal combination of porosity, pore size, and macroscopic design to achieve effective vascularization, bone formation, and mechanical performance in CSBDs. The variability in study designs, animal models, and outcome measures further complicates comparisons and limits clinical translation.