## 1 Introduction
In a study on the relationship between material resilience and hardness, a scraping experiment was conducted, and the results revealed the relationship equation between theoretical cutting depth and real cutting depth. The study verified that the equation can be applied to the cutting of both metal and polymer materials [20]. [PERSON] et al. [21] performed cutting using a micro milling cutter with a diameter of 0.2 mm to fabricate a copper column with a size of 30 \(\times\) 30 \(\times\) 320 \(\upmu\)m\({}^{3}\) (aspect ratio of 10.6) and then used scraping to investigate the relationship between the feed rate and amount of springback. [PERSON] et al. [22] conducted a test on copper materials with different crystallization directions and discovered that the scraping speed of 333 nm/s achieved the highest cutting depth and lowest springback. The springback was also dependent on the crystallization direction. [PERSON] et al. [23] investigated the resilience of polymer materials, using a micro-end mill (the edge of which had a radius of 48 \(\upmu\)m) to conduct an undercut experiment on acrylic materials. They discovered that, under various cutting depths, when the springback direction was vertical to the cutting tool feed direction and the cutting depth was smaller than 15 \(\upmu\)m, the springback rate was 100% and almost no chips were produced. When the cutting depth was larger than the cutter edge radius, the springback rate was approximately 30%. [PERSON] et al. [24] performed cutting on polymer materials with different glass transition temperatures by using a diamond cutter and different feed speeds. When the feed speed was increased in the early cutting period, the surface roughness was improved considerably. However, as the feed speed was increased further, the chips were removed though breaking; removal of the original material resulted in poor surface roughness. [PERSON] et al. [25] conducted a cutting experiment on injection-molded high-density and low-density polyethylene by using a grinding machine and various cutting speeds. The results revealed that, when the cutting speed was increased by 30,000 mm/min, the high-density polyethylene had higher mechanical strength and surface quality than the low-density polyethylene. However, even higher cutting speed resulted in chip breaking, which in turn caused lower surface quality. The temperature elevation during cutting also led to softening of the polymer material. In a study using PLA to produce biomedical stents, a CO\({}_{2}\) laser was employed to fabricate poly-l-lactic acid (PLLA) and PLLA/polycaprolactone/triethyl citrate stents. The simulation prediction and mechanical property testing results revealed that the stents produced using PLLA had the mechanical properties required for degradable stents [26]. [PERSON] et al. [27] used a CO\({}_{2}\) laser to produce poly (lactic acid-co-glycolic acid) and PLLA stents. They discovered that, by using the CO\({}_{2}\) laser, they could obtain small conicity of the side wall of the stents. Regarding the mechanical property, because a large heat-affected zone existed during CO\({}_{2}\) laser processing, the Young's modulus of the stents was 37% larger than that of the stents produced using excimer laser machining. Using electrospinning, [PERSON] [28] created artificial blood vessel cell growth stents with different directions of fiber arrangement at various collection speeds by using solutions of different proportions of PLA and polycaprolactone. The inner diameter, outer diameter, and wall thickness of the stents were 4.1, 5, and 0.45 mm, respectively. In addition, [PERSON] [29] employed circular heat transfer technology to fabricate PLA into a plate shape, which was then rolled into a round tube. The round tube was subsequently used in a circular transfer system to produce cardiovascular stents with a diameter of 10 mm and thickness of 0.7 mm.