## 1 Introduction  
Over the past few years, additive manufacturing has been developing rapidly. As technology advanced, 3D printing gained popularity, particularly in the areas of filament and metal powder printing. The application of additive manufacturing methods has been found in various sectors of industry, for example, including the automotive, aerospace, shipbuilding industries [1, 2]. Additive manufacturing has also found applications in medicine. By recreating the complex structures of organs and bones, doctors can plan operations with greater precision, increasing the safety and effectiveness of procedures [3]. One of the key fields in medicine is biomedical engineering, which has gained significant importance in recent years due to advances in 3D printing technology. Increasingly, the creation of personalized orthopedic implants tailored to specific fractures and dysfunctions of patients, including both humans and animals, is being pursued [4, 5, 6, 7, 8, 9]. Implants were designed based on images obtained from X-ray or computed tomography (CT) scans, utilizing advanced 3D modeling algorithms and computer simulations. This approach allows for a precise replication of the patient's anatomy and optimization of the shape and structure of the implant, improving its strength and tissue integration. [10, 11, 12, 13, 14]. In the design of orthopedic implants, an important element is to ensure adequate surface roughness, which promotes osteoblast settlement and aids integration of the implant into the bone tissue. On the other hand, in cases where implants are subjected to loads and abrasion, it is necessary to achieve smooth, polished surfaces to minimize friction and material wear, which has a decisive impact on the durability and functionality of the implants in long-term use. Currently, two of the most used methods for manufacturing implants using 3D printing are Selective Laser Melting (SLM) and Direct Metal Laser Sintering (DMLS). The SLM method involves selectively melting metal powder with a laser, allowing for the creation of fully dense, homogeneous structures. In contrast, DMLS is a process where fine metal powder particles are gradually fused together by a laser, leading to solid connections between the particles. This method also relies on layer-by-layer printing, but focuses more on sintering, enabling the production of more complex geometries [15; 16; 17; 18; 19; 20]. Three-dimensional printing from metal powders, particularly used in the manufacture of medical implants, requires precise control of the process parameters to ensure that the printed components have the right mechanical and structural properties. Key parameters include the power of the laser beam, the speed of the print, and the degree of structure fill. Another commonly used method in implant manufacturing is Powder Bed Fusion (PBF) [21; 22]. Using modern materials, such as biocompatible metal alloys (Ti6 Al7 Nb, Ti13 Nb13 Zr) and polymers (PEEK), enables the creation of implants that not only meet strength requirements but also physicochemical properties. In particular, the most used biomaterial to produce personalized implants is the titanium alloy Ti6 Al4V [23; 24; 25; 26; 27]. This alloy is characterized by a favorable combination of mechanical, physicochemical, and tribological properties. It primarily consists of titanium with the addition of 6% aluminum and 4% vanadium [28]. This alloy has found extensive applications in the production of orthopedic implants, such as joint prostheses (permanent implants), and stabilization plates (temporary implants) [29; 30; 31; 32]. It exhibits high strength while maintaining relatively low material density. As a result, implants made from this alloy do not cause rigidity in the skeletal system, thereby preserving proper biomechanics during movement. The properties of the Ti6 Al4V alloy, such as its long service life within the body, minimal risk of allergic reactions, resistance to pitting corrosion, and high strength, make it an ideal material for medical applications.