## 1 Introduction  
The field of prosthodonics, driven by an aging population, the desire for improved quality of life, and aesthetic considerations, represents one of the most rapidly advancing areas in dentistry today. Prosthodonics focuses on the replacement of missing teeth to restore both function and aesthetics. A primary limitation of dental implantation, however, lies in the condition of the jawbone, which significantly influences the success of the procedure. In many cases, bone reconstruction is required prior to implant placement to ensure optimal outcomes. A modern approach to address this challenge involves the application of guided bone regeneration (GBR) and guided tissue regeneration (GTR) techniques. These methods utilize a membrane that acts as a scaffold for bone tissue regeneration, providing both mechanical support and a conducive environment for tissue growth. The procedure typically involves exposing the targeted area, thoroughly cleansing it, and applying the membrane. This membrane functions as a barrier, preventing the infiltration of rapidly proliferating epithelial and connective tissue cells, as well as pathogens, thereby creating favorable conditions for bone growth to fill the defect [1; 2; 3; 4; 5; 6; 7]. Currently, the most commonly used membranes for guided bone regeneration (GBR) and guided tissue regeneration (GTR) are composed of poly(tetrafluoroethylene) (PTFE) or collagen. However, these materials possess certain limitations that necessitate the development of superior alternatives. PTFE membranes are biocompatible, stable, and mechanically durable. However, they are non-bioresorbable, requiring additional procedures for removal, which can cause patient discomfort and may potentially damage newly formed tissue. On the other hand, collagen-based membranes, while bioresorbable and biocompatible, exhibit low mechanical strength and unpredictable resorption rates, which can compromise their performance [8; 9; 10; 11; 12]. Synthetic biodegradable polymer membranes, such as those made from poly(lactic acid) (PLA), are also available. However, PLA membranes often exhibit low hydrophilicity, which limits tissue adhesion and osteoconductivity. The incorporation of functional additives into PLA membranes could mitigate these drawbacks and enhance their performance. Additionally, nanofiber membranes, owing to their high porosity, increased surface area, and improved mechanical strength and elasticity, offer enhanced placement stability and superior barrier properties [13; 14; 15; 16; 17; 18; 19; 20]. Electrospinning is a widely utilized technique for producing nano- and microscale polymer and composite fibers under high voltage. This technique involves two primary methods: using a polymer or composite dissolved in a highly volatile solvent or employing a thermoplastic polymer in a liquefied state. Fiber characteristics are significantly influenced by process parameters, such as applied voltage, needle-to-collector distance, solvent type, flow rate, and temperature. Moreover, because electrospinning can be performed under ambient conditions, it preserves the biological activity of thermolabile compounds. Post-treatment techniques can further enhance material functionality, and the process offers the advantage of reducing reliance on toxic solvents [21; 22; 23; 24; 25; 26; 27; 28]. Periclase, the highly crystalline form of magnesium oxide, is notable for its chemical stability and inertness, distinguishing it from its amorphous counterpart. Periclase nanoparticles possess antibacterial properties and, when incorporated into polymer matrices, enhance mechanical strength. Magnesium itself plays a critical role in influencing bone density and structure. Studies have demonstrated that magnesium oxide (MgO) nanoparticles significantly improve osteoblast adhesion and proliferation. PLA has gained significant attention in bone tissue engineering due to its favorable characteristics, including biocompatibility, biodegradability, and customizable mechanical properties.