Octopod core shell nanoparticles4/18/2023 Metoclopramide hydrochloride (MCA) was loaded in these systems as a model drug, and the encapsulation efficiencies were 59.96 ± 13.82% and 66.52 ± 2.23% each. Using this technique, hydrophobic shells with a gel core were produced, such as alginate–PLGA microparticles (Alg–PLGA MP) and alginate–PLLA microparticles (Alg–PLLA MP) ( Figure 1). Thus, a single-step fabrication technique was designed, which is called concurrent ionotropic gelation and solvent extraction. Fabrication of such a system is time-consuming and requires multiple steps. Similarly, composite hydrogel–PLGA particulate systems are designed to have a hydrogel core which efficiently loads hydrophilic drugs and a polyester shell which limits the rate of drug diffusion via limiting the water influx rate. The F127 core group showed very slow release at first, but as F127 swelled and cracked the microcapsules, the drugs were rapidly released, which makes them appropriate for delayed release. The LP powder group demonstrated a slow release rate at first, but increased burst release was observed over time and the peak concentration was reached at day 14. The in vitro study revealed that microcapsules with water core had a short release period (up to 16 d) while 5% gelatin core showed a stable release profile (up to 30d), which makes it more suitable for sustained drug release. For the inner phase, water, 5% gelatin, 25% Pluronic 407 (F127), and losartan potassium (LP) powder were used. designed PLGA microspheres with gel cores to obtain high encapsulation efficiency for small and highly soluble drugs. The core–shell particles have been used more frequently in drug delivery owing to the synergistic effect. To overcome this issue, additional functional layers, like hydrophilic gels, are included to the PLGA core–shell microspheres, and methods like coaxial electrohydrodynamic atomization (CHEDA) are practiced. The main challenges of using PLGA microspheres are reducing burst release and increasing encapsulation efficiency of hydrophilic drugs. These characteristics are highly dependent on the microsphere’s shape, size, surface, and thickness. The performance of the designed DDS is commonly assessed by their drug encapsulation efficiency, loading capacity, release pattern, degradation, and other factors. Targeting can be done by direct injection, receptor attachment, or the addition of nanoparticles that respond to certain bioenvironments. The nano/microparticle-based DDS process can be summarized into two steps: targeting the drug delivery site and releasing the encapsulated agent at the desired time and rate. In the tissue regeneration section, we especially include bone, cartilage, and periodontal regeneration. In this review, we summarized the current state of core–shell nano/micro PLGA particles for drug delivery, cancer therapy, and tissue regeneration. However, a smaller number of reviews have been reported on the PLGA core–shell microsphere. As per our knowledge, several review literatures have been published related to PLGA microspheres for biomedical applications. Strategy that sequentially releases growth factor and differentiation factor is commonly used. Microspheres up to 100 μm are said to be suitable for these cases. Some application examples include bone regeneration, cartilage, and periodontal regeneration. Core–shell microparticles are also applied to tissue regeneration, as an alternative solution for transplanting and autologous cell therapy. Microspheres are often targeted to cancer cells by adding receptors to the outermost layer or by making them respond to cancer-specific extracellular environments. Like other applications, two or more cancer treatment methods are frequently combined to seek synergistic effects. Cancer therapy using PLGA microspheres includes chemotherapy, photothermal therapy, hormonal therapy, immunotherapy, and others.
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