Since their introduction five decades ago (Bishara & Andreasen, 1970), clinical orthodontic treatment has extensively employed force-generating elastomeric modules, composed of polyurethanes manufactured from either polyether-or polyester-based subunits (Wong, 1976), for tooth movement. Manufacturers have considered the formulations of these products to be proprietary information and do not disclose exact compositions (Young & Sandrik, 1979). The use of these modules in the form of elastomeric chains attached to individual teeth minimizes the need for patient cooperation, favouring their incorporation by clinicians in the treatment protocol. These orthodontic elastomeric polymers are viscoelastic materials whose mechanical properties are dependent upon the conditions under which they are tested, specifically the rate of extension and the length of time extended (De Genova et al., 1985; Kovatch et al., 1976; Powers & Sakaguchi, 2006). Once activated, an elastomeric chain immediately begins to experience considerable force decay. In vitro experiments show that the greatest force losses per unit time occur within the first hour (Andreasen & Bishara, 1970; Wong, 1976). Orthodontic elastomers tested in water at 37°C have experienced over 40% force loss after 1 h and over 50% loss after 1 day (Andreasen & Bishara, 1970;