## 1 Introduction  
The introduction of the osseointegration concept by [PERSON] et al. [1], led the research toward the \"process whereby clinically asymptomatic rigid fixation of alloplastic materials is achieved and maintained in bone during functional loading\". Attention has then been focused on how to enhance the connection through material preparation and surface modification to achieve osseointegration: Topographic modifications through blasting with ceramic particles/acid etching and chemical modifications through titanium plasma spraying, electrochemical anodization, and calcium phosphate coatings have been proposed [2]. Among these surface treatments, combined etching and sandblasting have shown the best results in bone apposition and removal torque [3]. Frequently, the treatments have the purpose of increasing implant to bone surface ratio, additionally, rough surfaceshave been demonstrated to activate osteoblast differentiation [4]. In particular, sandblasted, large grit, acid-etched implant surface (SLA) treatment reformed the same topography surface shaped by osteoclasts and the osteoblast response observed on this surface is comparable to the response on surface conditioned by osteoclast [5]. Bioactive materials are now studied, bioceramics, ions, biomolecules, to determine whether osseointegration would be achieved, how efficiently, and with what effect [6]. Engraving the surface is not enough to increase biological contact: The benefits derived from micro-porosity and roughness can be enhanced by paying attention to wettability [7]. This property steered both the adsorption of proteins and the contact between blood cells and implant by activating a different healing pattern [8]. It was noticed that hydrophilic surface promotes the differentiation of MSC in osteoblasts and stimulates the secretion of large quantities of anti-inflammatory cytokines [9]. Accordingly, achieving complete hydrophilicity is the goal to increase the success of implant therapy. Several methods have been proposed to increase wettability and obtain hydrophilicity that is featured mainly at 0\({}^{\circ}\)-5\({}^{\circ}\) contact angle (CA). N\({}_{2}\) rinsing had a surprising effect on the implant surface: First, thanks to the extreme purity of the surface, the dynamic contact angle (DCA) was modified from 138\({}^{\circ}\) to 0\({}^{\circ}\)[10], turning hydrophobic surface into completely hydrophilic one, second the possibility of bonds with blood proteins is greatly increased, making the healing favorable [11]. UV light activation [12] or nonthermal atmospheric-pressure plasma using different gases [13] had interesting outcomes both on hydrophilicity and decontamination. Hydrophilicity is mainly influenced by roughness and chemical inhomogeneities of surfaces [14] and high interfacial energy [15]. The roughness influences wettability because when exposed to the air, the smallest micropores on the implant surface trap air leading to different conditions lowering the wettability. Therefore, in order to maximize wettability, roughness indentation must be hierarchically structured [16]. Dental implant surface energy is initially extremely high because titanium oxide is produced when titanium is in contact with atmospheric oxygen [17]. Nevertheless, the adsorption of atmospheric hydrocarbons, caused by the high surface energy, lowered the interfacial energy in time-dependent manner and consequently the wettability, turning the surface from hydrophilic into a hydrophobic one [18]. Preventing loss of surface energy in order to preserve wettability has been a crucial aspect and an important research topic in recent years. [PERSON] and [PERSON] [19], in 1988, underlined the advantages of storage in water titanium dental implant to maintain energy surface. This evidence led to the SLAActive (Sandblasted, Large grit, Acid-etched, Activated surface) technology, with the immersion of an SLA surface in a saline solution [20].