## 1 Introduction  
An arteriovenous fistula (AVF) is a surgically created passageway at the wrist that joins the arteries and veins for hemodialysis treatment for patients with end-stage kidney disease. Compared with central venous catheters (CVCs), AVFs have lower mortality and reintervention rates, and therefore, they are the best option for patients with end-stage renal disease requiring hemodialysis [1, 2]. At present, the success rate of AVF maturation is the main issue after AVF surgery. In approximately 30-40% of patients who have received an AVF operation, the vein fistula cannot successfully mature to achieve the blood vessel diameter and wall thickness required for hemodialysis in three months [3]. [PERSON] et al. [4] conducted a clinical study on AVF maturation, and their analysis indicated that vein diameters in AVF procedures that failed to mature were in the 3.6-4.2 mm range. Greater vein diameters have higher maturation success rates; AVF surgery is not appropriate for veins with diameters smaller than 2.5 mm [5, 6]. [PERSON] et al. [7] performed juxta-anastomotic stenting (JXAS) with nitinol self-expandable stents, using a 6 Fr (2 mm) catheter to insert a metal stent into the arteriovenous anastomosis from the venous side; the results indicated that this method could effectively increase the rate of the patient's AVF successfully maturing. Compared with balloon-expandable stents, self-expanding metal stents are more flexible after expansion and can avoid being damaged by external forces from the outside of the arm [8; 9]. However, in current clinical treatments, physicians rarely consider using metal stents to assist with AVF maturation, mostly because, after the three months of fistula maturation, the stent remains inside the body for a long time, leading to the risk of vascular occlusions or serious complications. Biodegradable stents offer the advantage of being metabolized by the human body over time, reducing the risk of complications associated with long-term stent presence and the need for a second surgery [10; 11; 12; 13; 14; 15; 16; 17; 18]. Biodegradable metal stents are primarily composed of magnesium (Mg), iron (Fe), zinc (Zn), and their alloys [19; 20; 21; 22]. Among these, magnesium alloys are widely used because of their well-documented performance and biocompatibility [19; 23]. However, their clinical application is constrained by rapid degradation, localized corrosion, gas generation during degradation, and low ductility and flexibility post-balloon expansion [23; 24; 25; 26]. Recent research on stent development has increasingly focused on biodegradable polymers, such as polylactic acid (PLA), which is derived from natural cellulose or starch [27; 28; 29; 30]. Its excellent biocompatibility has been validated, and it has been employed in cardiovascular stents for many years [31; 32; 33]. Currently, PLA vascular stents in practical applications are predominantly balloon-expandable [31; 32; 33; 34; 35; 36]. However, this approach results in reduced flexibility and an inability to withstand significant mechanical deformations after expansion. Research into self-expanding PLA stents or modified PLA materials for such applications remains limited [37; 38]. The primary challenge lies in the fact that shape-memory self-expanding PLA stents struggle to generate adequate radial force for vascular expansion after deployment and face difficulties being crimped into a small-diameter delivery system. Addressing these challenges requires innovative design or material modification approaches to enhance the functionality and feasibility of self-expanding PLA stents. The current manufacturing method of PLA stents is to use injection molding or extrusion molding to make the PLA tube of the stent and then use laser processing to cut the tube into the required geometric structure [39; 40; 41; 42]. However, new molds must be designed for the injection molding or extrusion of tubes or stents.