Indomethacin (IND) is used as a model drug for the development of novel sublingual drug delivery approaches. This nonsteroidal anti-inflammatory drug is commonly used as a painkiller with an oral administration to reduce fever and swelling, as well as a medication to treat rheumatoid arthritis or osteoarthritis due to its strong action and high therapeutic efficacy in the body . However, at the same time, its short half-life time and the associated repeated oral administration result in toxicity-issues toward the digestive system and kidneys as well as malaises like nausea, stomach pain, and diarrhoea which could be expected to be reduced by using sublingual delivery system. Maintaining drugs in their amorphous state improves the dissolution rate and oral bioavailability. However, some limitations including recrystallization due to the physical instability of the amorphous state and residual micro-crystallinity of the drug can cause problems such as patient-to-patient variability. This can be addressed and overcome via preparation of amorphous solid dispersions (ASD) using suitable excipients, e.g., through tuning the interactions between polymeric excipients and drug. One well-known and widely used method to fabricate ASDs is hot melt extrusion (HME). This method involves melting and intensive mixing of the drug into the polymer matrix, resulting in the formation of a single phase. There are numerous well-known and well-studied polymer excipients for the preparation of ASDs , such as poly(2-ethyl-2-oxazoline) and its structural similar polyvinyl pyrrolidone resulting in a better performance of the 2-oxazoline based polymer . The selection of an excipient is not only based on the processability using a given method and the possibility of designing a controlled release from the amorphous formulation, but also the miscibility and possible interactions between drug and polymer play an important role. Previously, poly(2-oxazoline)/poly(2-oxazine) triblock copolymers have been employed very successfully in high drug loading formulations with up to and more than 50 wt.% of drug. Also, diblock, random and gradient copolymers from poly(2-oxazoline)s/poly(2oxazine)s have been investigated as potential excipients and some systems also allowed high drug loadings. Depending on the properties of the chosen polymer and drug, the drug loading capacity can be changed and adjusted to the required needs. An amorphous blend facilitates a faster dissolution and drug release compared to crystalline drug loaded material, due to its higher free energy achievable for example using melt processing techniques such as previously mentioned HME. Furthermore, drug delivery systems with a high surface area to volume ratio are also beneficial and favourable, because they can provide a high capacity of drug loading in addition to a fast dissolution due to their highly porous design. Solution electrospun fibers containing drugs are already well studied as fast sublingual drug delivery systems due to their high surface area and exceedingly small fiber diameters showing great potential for this application. In addition, they provide faster dissolution compared to films; however, the electrospinning technique requires (often toxic) solvents and the processed fibers are randomly oriented , limiting the degree of control over the morphology. Another method capable of producing fibers within the lower micron-range is called melt electrowriting (MEW), which electrostatically draws a polymer melt out of a syringe onto a computer-controlled moving collector without the need of (toxic) solvents. MEW is a high resolution additive manufacturing (AM) technology allowing accurate microfiber placement with fiber diameters commonly ranging between 5 µm to ~ 50 µm and production of unique printing patterns, as well as highly porous microfiber scaffolds. This technique uniquely fills the fabrication gap between solution electrospinning and melt extrusion-based direct writing. The former produces sub-micron fibers with chaotic and uncontrollable fiber placement, while the latter allows good fiber placement but generates larger diameters, typically well of above 100 µm. The high porosity and larger surface area of the MEW scaffolds compared to films or other 3D printed constructs benefits the use in a variety of biomedical applications, including tissue engineering and drug delivery .