## 1 Introduction  
Vascular stents are tiny mesh-like devices that are placed into an obstructed artery to open the lumen and allow smooth blood circulation [1]. Based on a stent's expansion method, stents are classified into two categories: balloon-expanding and self-expanding. Materials such as 316L stainless steel, L605 CoCr alloy, and polymer are used for manufacturing balloon-expanding stents. NiTi alloy is used for manufacturing self-expanding stents, given its superior elastic and shape memory properties. In recent years, CoCr alloy has gained interest due to its excellent radial strength and, therefore, its ability to produce extra-thin struts with increased strength [2]. They are also MRI (Magnetic Resonance Imaging) compatible as well as radiopaque. The design of stents is complex and, as they are very small, precise manufacturing processes are necessary. Because of the non-contact, precise, and localized energy inputs [3], 3D laser profiling has become the primary choice for stent cutting. Considerable research has been conducted on neodymium-doped yttrium aluminum garnet (Nd:YAG) laser cutting of stents. [PERSON] et al. [4] described the precision manufacturing of stainless steel stents using a Nd:YAG laser, and a noticeable heat-affected zone (HAZ) was detected in the cross-sections. To minimize the HAZ size, optimized process parameters (a high repetition rate and short pulse width) were suggested. [PERSON] et al. [5] investigated the Nd:YAG laser cutting of NiTi alloys and studied the influences of process parameters on cutting quality. The detected HAZ size ranged from 6 to 30 \(\upmu\)m. Embrittlement in the HAZ can lead to microcracks and shorten a stent's fatigue life, as described by [PERSON] et al. [6]. [PERSON] et al. [7]reported the Nd:YAG laser cutting of CoCr stents, and a strut width dimension error of \(\pm 15\)\(\upmu\)m was detected. [PERSON] et al. [PERSON] et al. (2017) cut 316 LVM stents using Nd:YAG lasers, and a strut dimension of \(150\pm 15\)\(\upmu\)m was achieved. The dimension error of struts can influence the stents' mechanical properties. In recent years, fiber lasers have been widely used in micromachining for higher beam quality, reliability, and process efficiency. Comparative studies on Nd:YAG lasers and fiber lasers have been conducted. Fiber lasers have been proved to have better cutting quality than Nd:YAG lasers in terms of kerf size, roughness, and HAZ. [PERSON] et al. [PERSON] et al. (2017) found that using fiber lasers can result in smoother cutting surfaces. [PERSON] et al. [PERSON] et al. (2017) demonstrated that cutting quality (HAZ and average roughness) was better with a fiber laser compared to an Nd:YAG laser. To further improve the quality of fiber laser cutting, [PERSON] et al. [PERSON] et al. (2017) introduced a water flow through the inner wall of the tube, which resulted in a narrower kerf width, lower surface roughness, less dress, as well as a smaller HAZ compared to dry cutting. Fiber lasers have also been used in manufacturing biodegradable stents. In the work of [PERSON] et al. [PERSON] et al. (2013); [PERSON] et al. (2013), microcutting biodegradable stents from AZ31 magnesium alloy with a Q-switched fiber laser in the ns-pulse regime, as well as inert and reactive gas cutting conditions, were compared. The study found that the laser microcutting of AZ31 Mg alloy required inert gas conditions, as opposed to reactive cutting with O\({}_{2}\). Defects, such as dress formation and HAZ, are always inevitable, because the mechanisms of long-pulse lasers include thermal heating, melting, and evaporating of base materials, as explained by [PERSON] et al. (2014). [PERSON] et al. [PERSON] et al. (2015) presented a framework for an experimental test of crystal plasticity micro-mechanics for the high-cycle fatigue (HCF) of micro-scale L605 CoCr stent material. Specimens were manufactured via laser cutting and the electropolishing (EP) method. EP was used to remove the HAZ during laser cutting and to provide a smooth surface.