Extensive efforts have been made to address the limitations encountered in the fabrication of tissue engineering (TE) scaffolds. Accordingly, PEDOT has been incorporated into biodegradable polymer matrices having high mechanical strength, biodegradability, and good solubility in various solvents . For example, several polymers, including polylactide (PLA) 25 , poly (methylmethacrylate) (PMMA) 26 , poly (vinyl alcohol) (PVA) 27 and poly caprolactone (PCL) have been utilized for this purpose. Among them, in particular, PCL has emerged as a prominent synthetic polymer for TE scaffolds due to its hydrophobicity, excellent thermoelasticity, and its ability to form polymeric blends . Moreover, the long degradation time of PCL under physiological conditions, resulting from the hydrolytic chain scission of the ester groups, aligns well with the timeframe required for tissue regeneration or healing (typically 2-3 weeks) . Another advantage of PCL is related to the ease of its synthesis, which involves ring-opening polymerization (ROP) of ε-caprolactone (ECL). Predominantly, pseudo-anionic pathway utilizing stannous octanoate (Sn(Oct)2) are preferred in these syntheses. However, cationic pathways are also performed using cationic initiators. Accordingly, in recent years, various synthetic approaches have been explored for PEDOT-PCL scaffolds. For example, chemical oxidative (co)polymerization of monomers (EDOT and ECL) using FeCl3 and stannous octanoate (Sn(Oct)2) in multiple-step reactions. 41, 42 In addition, electrooxidative polymerization of macromonomers, such as PCL-substituted EDOT, utilizing potentiostats , and physical blending of PEDOT/PCL by (electro)spinning or by vapor-phase polymerizations (VPP) are employed . Although these methods are effective to some extent in the fabrication of scaffolds, they generally involve the use of corrosive chemicals and/or require high energy input or sophisticated experimental setups.