## 1 Introduction  
Fabrication of 3-D construct or macro scaffold by additive manufacturing technologies, such as stereolithography [1], deposition and layering [2], silicon micromachining [3], 3-D printing [4], and selective laser sintering (SLS) [5], has garnered interest in recent years. However, the SLS printing method uses simple operation, adaptation from the patient's scanned image to the computer aided design (CAD) model, and easier customization of the scaffold for the generation of the CAD model [6, 7, 8]. SLS printing has also made it possible for tissue engineers to fabricate anatomically customized tissues and to develop functional scaffold with enhanced nano-detailed features for efficient cell guidance and growth [9, 10, 11]. With SLS printing, the binding of the polymer does not require any toxic components [12]. The material selection is critical for structural and mechanical support. For instance, surface properties facilitate cell attachment and migration within the matrix and mass transport while maintaining cell-matrix interaction [13; 14]. This fabrication method, which allow engineering whole organs and large tissues, offers an advantageous transforming paradigm of tissue engineering. One important requirement for the scaffold development is the porosity, which plays an important role by creating a larger surface area-to-volume ratio and aiding in cell growth. Porosity of the scaffold can be tuned by varying the pore size and strut thickness using the SLS fabrication method. To the best of our knowledge, very few studies have reported specific details about scaffold strut thickness [15]. In the SLS technique, the porosity of the scaffold can be enhanced by the porogen leaching method, which gives rise to porous scaffold. [PERSON] et al. reported a pioneering methodology for lotus-shaped scaffold fabrication with interconnected branching channels. They used polylactic acid and salt particles, and the salt particles were leached out using water [16]. Previously, the use of sodium chloride (NaCl) as a porogen for the fabrication of PCL/NaCl using the SLS technique was also reported [12]. However, NaCl has high thermal conductivity, which leads to growth of the struts due to heat conduction into adjacent powder particles [15]. The growth of struts affects the precision of the printing, reducing the high accuracy of the intended design. Therefore, it is essential that the particle has low thermal conductivity to reduce heat conduction, thereby increasing the accuracy of the printing of the module. Additionally, remnants of NaCl salt particles within the scaffold may affect the cellular osmolarity. This technical limitation can be overcome using polyglycolic acid (PGA). It has low thermal conductivity, ideal cell affinity, workability and mature clinical application [17]. The construction of the in vitro liver model as an attempt to study and recapitulate the physiological condition has evolved in liver tissue engineering [18; 19]. However, one of the major obstacles is the risk of thrombosis development [20]. An implantable tissue construct should overcome the problem of blood compatibility, which is not well understood [21]. Interaction with blood leads to various pathophysiological processes, including adsorption of plasma protein on the surface material [22], platelet activation, aggregation, and adhesion [23]. These processes build up to thrombosis, one of the most severe events and challenging aspects for engineering clinical transplantable liver tissue [24]. Different methods can be employed to assess hemocompatibility of blood contacting tissue engineered scaffold, such as calculation of hemolysis %, platelet deposition and aggregation counter, surface analysis of platelet adhesion, and determination of complement system molecules [25]. According to [PERSON] et al., platelets are deposited and interact through integrin receptors on the cell surface, allowing for their adhesion. Adherence of the platelets leads to the release of coagulation factors, causing thrombosis.