## 1 Introduction  
Contemporary medicine uses the knowledge and possibilities of modern engineering extensively. This is significantly reflected in the field of the replacement of damaged bone segments [1]. The implants must meet special demands; therefore, they must be produced from the highest quality materials by using the most modern production technologies [2]. The implant properties are required to be as similar to the original biological bone as possible. Material must cause any problems for the patients and help them to live a full life at the same time [3]. Therefore, implants are expected to be biocompatible to the human body, able to perform their function for a long time, durable, easy-care, and maintainable [4]. Metallic materials are the best choice for most bone replacements [5]. Titanium alloys appear to be very attractive, mainly due to their low weight compared to other metals, favorable biocompatibility, and corrosion resistance. The downside of titanium alloys is the relatively high Young's modulus (113 GPa) compared with human cortical bone (15 GPa to 20 GPa), which may adversely affect the healing process even for patients with a proper bone density [6]. Based on the fact that the reduction of \(\alpha\)phase in titanium alloys diminishes Young's modulus, [PERSON] et al. designed and tested \(\beta\) phase titanium alloy with Young's modulus around 65 GPa [7]. For instance, [PERSON] et al. enriched the titanium alloy with ceramic material hydroxyapatite (HA) to reduce Young's modulus. Moreover, an increase in the biological activity of titanium was observed from in vivo and in vitro tests due to the introduction of HA [6; 8]. [PERSON] et al. performed compression and bending tests on porous titanium implants with a biomimetic calcium phosphate (CaP) coating to evaluate their mechanical properties [9]. Porous structures have several indisputable advantages, from reducing the weight of the implant while maintaining satisfactory mechanical properties to improving the osseointegration process and overgrowth of biological bone in the implant after its implantation into the body [10]. For fabrication of certain structures, additive manufacturing (AM) appears to be a very promising technique [11]. Technologies such as selective laser sintering (SLS), direct metal laser sintering (DMLS), and electron beam melting (EBM) operate on the principle of using high-power lasers to create mechanically effective structures [12; 13]. SLS technology uses layer by layer building strategy defined in a predesigned computer-aided design (CAD) model [14]. The metal powder with a size of 20 \(\upmu\)m to 100 \(\upmu\)m is stored in a container from which it is applied in the vertical direction to the construction platform by a roller [15]. The whole process is carried out under an inert atmosphere (e.g., argon or nitrogen) to prevent oxidation and contamination of the powder during sintering. The surrounding unsintered material serves as a support for further layers and can be recycled at the end of the production process. For a detailed analysis of sintered porous material, the method of computed tomography (CT) as a nondestructive examination technique is appropriate to use. CT can be utilized for grain size, porosity and geometric analysis, defects identification, and structural evaluation [13]. The manufactured components require heat, machining, and polishing postprocessing treatment [16]. According to [PERSON] et al., there is a great potential of AM in the production of dental implants. In their study, experimental porous Ti alloy dental implants, made by using DMLS, exhibited more bone formation than commercial implants [17]. Correspondingly, the results of the recent preclinical meta-analysis indicate that bone formation is improved when porous surface dental implants are used, compared to non-porous surface implants [18]. Structural factors in implants, including porosity level, pore size and pore interconnectivity, affect bone tissue ingrowth and differentiation.