## 4 Discussion
This condition is formed from surface modification with a polymer [35; 36; 37; 38]. Furthermore, the nano-surface is known to transfer stress uniformly [34]. The main problem when implants replace missing teeth is that their mechanical properties are not identical with the bone and the teeth being replaced. Implants with higher elastic modulus will adsorb all the load, which creates a stress shielding effect and leads to bone loss [33]. According to the nano-indentation analysis, the Young's modulus of the IDCT-Ti/GRGD-1 surface was equivalent to cortical bone (-20 GPa), which would reduce the stiffness of the implant and prevent bone resorption around the implant [13; 33; 39]. The hemocompatibility assay of the IDCT-Ti/GRGD-1 implant revealed that the amount of RBC aggregation accompanied the presence of copious fibrin. This result is markedly different from our previous study using IDCT surface-modified implants without peptide involvement. The IDCT-Ti implant had less fibrin than the IDCT-Ti/GRGD-1 implant [13]. Fibronectin is required by fibrinogen to assemble in the ECM [40]. The presence of fibrinogen will cause the ECM to mediate cell migration and restore the matrix during tissue repair [21]. Fibrin will support the wound healing process, both soft and hard tissues, which will consequentially affect the osseointegration [7; 41]. The soft tissue healing will create a physical seal on the bone around the implant, protecting from oral environment contamination such as bacteria [41]. Since implant placement causes injury in the jawbone, it will induce wound healing as hemostasis and coagulation, granulation of tissue formation, bone formation, and remodeling [42]. The good hemocompatibility is related to the wettability, which allows the absorption of various biological fluids, proteins, and cells [13; 29]. The wettability of the IDCT-Ti/GRGD-1 implant using a water test is in line with our previous study, which was obtained from the involvement of super hydrophilic PF127 on the surface-modified implant with IDCT [13]. In the current study, the wettability measurement was not only performed using deionized water, but also using blood. Both fluids have a different viscosity, with a blood viscosity (3.49 cPo) higher than water (1 cPo) [43]. Indeed, lower viscosities are more absorbable compared to higher viscosities. Moreover, blood is the fluid that first makes contact with the implant, and the osseointegration begins [44; 45; 43]. A surface is hydrophilic if it has a contact angle of less than 90\({}^{\circ}\), super hydrophilic if it approaches 0\({}^{\circ}\), while a surface is hydrophobic if the contact angle exceeds 90\({}^{\circ}\), and superhydrophobic if it is higher than 150\({}^{\circ}\)[46; 47]. The present study has found that the contact angle pattern of blood is similar to water, which is close to 0\({}^{\circ}\). The SLA implant reveals hydrophilic surface properties when subjected to a water test, whereas when using blood, the SLA implant is almost superhydrophobic. Contrarily, another study also used blood to assess the wettability, and it was found that the contact angle at the SLA-treated implant was about 27\({}^{\circ}\)[44]. The difference in results may be due to the measurement of the contact angle performed on flat discs, which cannot represent the actual implant surface [46; 47]. Furthermore, wettability is closely related to surface energy; a lower contact angle indicates high surface energy, which means it can allow the liquid to spread and adhere more widely to the implant surface [47; 48]. Ossoeintegration can be assessed through intraosseous implant stability using X-ray [14; 49]. In this study, the absence of radiolucency as a sign of bone resorption surrounding the implant demonstrates the stability of the intraosseous implant that was observed 6 months after placement. The quality and quantity of bone, and the location of implant placement in the jaw, also determines the success of the dental implant [50].