conditions to maintain the scale of medical device manufacturing; and 4) the treatment must not incorporate antibiotics to maintain global antimicrobial stewardship efforts. The zwitterionic polymer polysulfobetaine (PSB) was selected as the antifouling component of the surface modification to benefit from its biocompatibility, ultralow-fouling properties, and oxidative stability. By adsorbing water electrostatically, PSB coatings form a thin hydration barrier that prevents organic materials from adhering to surfaces. [22] Commonly used approaches to attach PSB coatings to surfaces, such as radical-initiated graft polymerizations of PSB-methacrylate necessitate the use of oxygen-free conditions, [23] preconditioning steps, [24] or long reaction times [25] that do not meet scalability requirements. To circumvent the use of air-free graft polymerizations, we employ perfluorophenylazide (PFPA) chemistry as a molecular anchor to link the PSB coatings onto the surfaces of polymeric materials under ambient conditions. When triggered with UV-light, PFPA moieties generate a highly reactive nitrene that forms covalent bonds with materials containing amines, CC double bonds, and CH bonds. [26,27] With this method, PSB is rapidly coated onto a broad range of substrates using UV light under ambient conditions with no preconditioning steps. Thus, many different medical devices may be quickly and conveniently treated on the manufacturing level.We first demonstrate the effect of the treatment on polydimethylsiloxane (PDMS) as an exemplary, extremely difficultto-modify model for a common elastomer used in implantable medical devices. [28] Commonly known as silicone, PDMS is widely used for its biocompatibility, good chemical stability, ease of fabrication using injection molding or extrusion, and low cost. [29][30][31] Many implantable device makers have moved away from classical medical elastomers and plastics such as latex and polyvinyl chloride due to allergens [32] or plasticizers [33] in these materials that leach out and often lead to irritation or complications. PDMS-based devices do not require plasticizers and have been shown to lead to fewer complications than latex and polyurethane-based devices. [34] Despite its ideal properties, the nonpolar nature of PDMS facilitates the adhesion of organic materials. Bacteria, platelets, proteins, and other biomolecules bind strongly to the hydrophobic surfaces of PDMS elastomers, leading to the colonization and proliferation of biofilms. [22] When common hydrophilic surface treatments are performed on PDMS, such as plasma oxidation, [35] UV-ozone, [36] or corona discharge, [37] the effects are short-term due to rapid hydrophobic recovery. The highly mobile chains of PDMS (glass transition temperature ≈ −120 °C) can reorient themselves to "hide" the surface modified elastomers, when exposed to air, within hours. [38] Other methods seeking long-lasting hydrophilic PDMS surfaces typically require preconditioning steps with silane [39][40][41] chemistry or radical polymerization. [...