Recently, the ability of natural phospholipids to self-assemble into organized membrane-enclosed structures has been mimicked by amphiphilic copolymers. These synthetic macromolecular amphiphiles form assemblies that are remarkably similar to biological analogues, such as vesicles, tubular myelins, and tissuelike structures. Polymeric amphiphiles have much higher molecular weights than phospholipids and can self-assemble into more entangled membranes, imparting improved mechanical properties to the final structure. Polymer vesicles or polymersomes can combine several different polymeric compositions provided that they have the correct hydrophile/hydrophobe ratio. Particularly interesting for biomedical applications are those copolymers that combine hydrophobic blocks with the nonfouling and nonantigenic properties of either poly(ethylene glycol) (PEG) or biomimetic poly(2-(methacryloyloxy)ethyl phosphorylcholine) (PMPC). Indeed, the macromolecular nature of such polymersomes offers several advantages compared to low-molecular-mass amphiphilic systems such as liposomes. PEG or PMPC polymersomes can be decorated by denser and higher molecular mass hydrophilic polymeric corona, with consequent longer circulation times than more traditional delivery systems such as stealth liposomes and other nanoparticles. In addition, amphiphilic copolymers have critical aggregation concentrations (i.e., the minimum copolymer concentration necessary to form colloidal aggregates) that are very low and, in some cases, essentially zero. Therefore, polymeric amphiphiles have very slow chain exchange dynamics, implying that they assemble into locally isolated, nonergodic structures. This means that such copolymer assemblies have very slow rates of dissociation, allowing the retention of the payload for very long time periods. Further, the absence of molecularly dissolved amphiphilic copolymers in solution avoids cytotoxic interactions with biological phospholipid membranes. These can range from complete biomembrane dissolution and therefore cell death, in the case of small-molecule surfactants, to more benign effects such as up-regulating the gene expression and altering cell genetic responses for low-molecular-weight copolymers. Responsive formulations have also been created to exploit the sensitivity of specific hydrophobic polymers to external stimuli such as pH, oxidative species, and enzyme degradation. These properties have recently encouraged the application of polymer vesicles as delivery vectors for bioactive molecules. One of the most technically challenging hurdles is the intracellular delivery of genetic materials (DNA, RNA, and other nucleic acids). These species are used to treat diseases by modifying gene expression within specific cells. Gene therapy requires vectors that can deliver genetic materials within the cell without compromising its integrity. To date, the most efficient gene vectors have exploited the natural ability of viruses to transfect cells. However, viral vectors can produce adverse systemic immune responses, including patient fatalities. Moreover, without further genetic engineering, the targeting efficiency is limited to the specificity of the virus. In vitro alternatives to viruses are based on controlled cellular membrane permeabilization via electroporation, ultrasound poration, or particle bombing. In contrast, in vivo synthetic vectors such as cationic lipids, cationic polymers, inorganic particles, and polymer-inorganic particle hybrids have been designed to condense DNA via electrostatic interactions. Unfortunately, not only do these condensation methods have very low transfection efficiencies compared to viruses but, since the nucleic acid encapsulation is based on electrostatic complexation, highly charged plasma proteins can compete with the cationic vector for nucleic acid binding, potentially displacing it. This translates into very short plasma circulation times with rapid hepatic uptake. Recently, it has been observed that both lipids and PEGylated lipids are not able to protect nucleic acids from enzymatic degradation, either outside or inside the cell. Herein we present the use of biomimetic polymersomes for gene delivery. We have used pH-sensitive poly(2-(methacryloyloxy)ethyl-phosphorylcholine)-co-poly(2-(diisopropylamiC O M M U N IC A TI O N