Other solutions include formulations based on a medium with modified density, _e.g._, a biodegradable chitosan/gelatin-based hydrogel that releases LTP over 7 days _in vitro_ designed for intravitreal injection [26]; a hyaluronic acid sodium salt/hexamethylene diisocyanate-functionalized 1,2-ethylene glycol bis(dilactic acid) hydrogel that releases the drug substance over more than 60 days _in vitro_ designed for subconjunctival administration [27]; a niosomal gel that releases LTP _in vitro_ in less than 50 h [28], eye drops in a hyaluronic acid-chitosan nanoparticle (_in vivo_ test) [29] or biodegradable/soluble DDSs for subconjunctival administration, _i.e._, poly(D,l-lactide) (D,l-PLA)/mPEG nanoparticles that releases LTP over nearly 14 days _in vitro_[30]; and phytantrol cubosomes that release LTP _in vitro_ over 1 day [31]. For topical injections, the gel form is slightly similar to a solution, while nanoparticles often do not provide an opportunity to introduce the appropriate dose of the medicinal substance, and the large surface area often results in a burst effect. It should be pointed out that continuous subcutaneous infusion of 0.005% LTP solution over 7 days using mini pumps inserted in the backs of adult male normotensive Wistar rats effectively lowered intraocular pressure [32]. The solid biodegradable formulations seem to be the most appropriate. Therefore, a biodegradable subcutaneous implant releasing LTP peripherally should also be considered. Poly(lactide-_co_-glycolide) (PLGA) copolymers have been proposed relatively often as carriers in ocular DDSs for a wide variety of drug substances. The properties of PLGA (50:50-75:25) copolymers allow the formulation of biodegradable DDSs administered via different routes (_i.e._, intraconjunctivally, intravitreally, or subconjunctivally) for drug substances with various physicochemical properties (_e.g._, mitomycin C, bromionidine tartrate, cyclosporine A, tacrolimus, and triacinolone acetonide). Such formulations ensure a prolonged release period measured in weeks rather than minutes or hours [33; 34; 35; 36; 37], which can significantly increase adherence. This represents a significant step forward for registered medicinal products. However, their administration may be associated with high invasiveness. Considering the above, in this study, a shape memory poly(l-lactide-_co_-glycolide-_co_-trimethylene carbonate) P(l-LA:GA:TMC) was used to design terpolymer matrices with LTP as a universal model administered intraconjunctivally, intravitreally, subconjunctivally, or subcutaneously. As a drug carrier, P(l-LA:GA:TMC) is a significant alternative to existing proposals based on PLGA copolymers because of its mixed degradation mechanism (_i.e.,_ bulk erosion and surface erosion) and possibly better control of drug release [38; 39; 40; 41]. It should be pointed out that for PLGA copolymers, the release patterns result from bulk erosion only [42; 43; 44]. Previously, it was revealed that formulations based on P(L-LA:GA:TMC) terpolymers ensured prolonged release without significant release deterioration of 17-6-estradiol [40], riseridone [45], and aripiprazole [46] as a result of the stable mixed mechanism of degradation. Moreover, the P(L-LA:GA:TMC) terpolymers possess the important mechanical properties required for ocular formulations. First, it is characterized by low stiffness and a ductile mode of deformation under mechanical stresses [46], which are important features for intravitreal, subconjunctival, or subcutaneous administrations. Second, the ability to return to its original permanent shape from a temporarily fixed shape upon exposure to a thermal stimulus has been proven previously [47]. Changing the shape and size of drug formulations appears to be particularly important for reducing the invasiveness of administering DDSs, especially by implantation. This study aimed to develop an LTP solid biodegradable delivery system based on P(L-LA:GA:TMC) with shape memory to reduce its invasiveness.