## 4 Discussion
studied the synthesis of CeO\({}_{2}\) nanoparticles at different heating temperatures (120 \({}^{\circ}\)C, 200 \({}^{\circ}\)C, 400 \({}^{\circ}\)C, and 600 \({}^{\circ}\)C) and concluded that with higher calcination temperatures, XRD peaks became sharper, attributing the enhancement of crystallinity to calcination temperature [51]. [PERSON] et al., ended up with the same results, observing that synthesized CeO\({}_{2}\) nanoparticles at different calcination temperatures (400 \({}^{\circ}\)C, 500 \({}^{\circ}\)C, and 600 \({}^{\circ}\)C) via the sol-gel method showed an increase in crystal size as the temperature increased. With the rising calcination temperature, the surface area of all samples decreased. The greater interparticle pore diameters for larger particles are reflected in the lower values for surface area. Despite differences in size, all samples exhibited a uniform spherical morphology. In the present study, at the highest Ce precursor/gelatin ratio the spherical shape was retained in the smaller particles, however, a more rectangular or irregular morphology was observed in the largest NPs (Figure 4). [PERSON] et al., synthesized ceria by the coprecipitation method at three different temperatures 350 \({}^{\circ}\)C, 400 \({}^{\circ}\)C, and 450 \({}^{\circ}\)C. The results revealed that with the elevation of temperature, the CeO\({}_{2}\) nanoparticles' crystal size increased. Also, the specific surface area seemed to be decreasing as grain size increased, which proves that temperature and crystallinity are proportional, since as one increased, so did the other [72]. [PERSON] et al. studied the crystallite growth in synthesized CeO\({}_{2}\) NPs under various calcinated temperatures. They concluded that as the calcination temperature increased, the smaller particles were progressively integrated into larger ones. Also, the calcination temperature increased the nanoparticles' crystallinity and average crystallite size [73]. Nanotechnology has aided in the prevention, rapid diagnosis, and therapy of many diseases as well as in the development of specific topographical surface formations, such as implant surfaces, with reliable tissue-integrated properties. Blood vessels are damaged during surgery, which causes implant surfaces to come into contact with blood components [28]. Thus, the initiation of potential negative effects on human health is a major worry with regard to the use of NPs in medicinal applications [80]. Designing and creating suitable nanomaterials that do not cause hemolysis and the formation of ROS following administration is an important issue for nanomedicine. The primary purpose of RBCs, which is based on their metabolic nature, is to carry oxygen to all tissues. Red blood cells are continually exposed to ROS under physiological circumstances. It has been noted that an accumulation of ROS in RBCs might degrade the properties and structure of hemoglobin, reducing its ability to carry oxygen [81]. Numerous investigations revealed that the physicochemical characteristics of NPs can cause erythrocyte damage [82; 83]. The erythrocyte membrane's oxidative damage is one process essential to hemolysis. Elevated oxidative stress results in cell damage since erythrocytes do not produce SOD and catalase, which are two essential enzymes for ROS scavenging. Various substances, including magnesium hydroxide, carbon-based nanoparticles [84], silver [85], and gold [86], have been examined for their hemolytic potential. Each of these compounds has a unique hemolytic property, highlighting the necessity of determining the vital hemocompatibility factors before applying these nanomaterials to medicinal applications. Particularly, the hemocompatibility of implants coated with NPs is a subject of considerable research. Titanium implants were coated with TiO\({}_{2}\) nanotubes, calcium phosphate coating, and a phospholipid (POPC) film by [PERSON] et al. According to hemocompatibility results, there were relatively low hemolysis levels on various implant surfaces.