In industrialized nations, sensorineural hearing loss is a common disease and is usually caused by a primary loss of auditory hair cells, which are the inner ear’s sensory cells. In addition to hereditary factors, acquired causes, such as increased noise exposure or the application of ototoxic drugs, play a crucial role in the development of sensorineural hearing loss.1,2 An effective treatment for damaged hair cells or for the regeneration of already degenerated sensory cells of the inner ear in humans is not yet possible. Instead, the prosthetic forms of therapy are performed to replace the damaged organ’s function. Severely impaired and deaf patients are treated by implantation of electronic inner ear prostheses called cochlear implants. Deaf patients treated with cochlear implants gain a renewed sense of hearing and have a greater opportunity to communicate using audible speech.3 This leads to improved social integration and a significant increase in the patient’s quality of life. Cochlear implants use a multichannel electrode that is inserted into the scala tympani to replace the function of the missing hair cells. Through the formation and transmission of spiral ganglion cell (SGC) action potentials, an artificially-generated sound impression is achievable. However, following the primary loss of hair cells, a progressive decrease in SGC density is observed.4 This is caused by missing electrical and neurotrophic stimulation, as well as other forms of stimulation.5,6 To achieve better speech recognition with cochlear implants, a high number of SGC must be ensured.6 A large number of neurotrophic factors have a protective effect on SGC after primary hair cell loss. The systemic treatment of inner ear diseases is complicated by the presence of the blood–cochlear barrier. Adequate drug levels are only reached through the application of very high drug doses, which leads to an increased risk of side effects. Through local application of neurotrophic factors, the progressive degeneration of SGC may be decreased. Important representatives of this substance group are brain-derived neurotrophic factor (BDNF), glial cell line-derived neurotrophic factor, and fibroblast growth factor.7,8 Nevertheless, continuous therapy is necessary because previous studies detected a progressive reduction of SGC after the cessation of therapeutical application of BDNF.9 The first attempts to produce continuous drug-delivery systems were realized using osmotic pumps. These pumps allowed continuous application periods into the inner ear for weeks. Because of delivery time limitations and the necessity of pump changes that would allow for longer application duration, this approach is not feasible for human therapeutic applications. Another option for chronic neurotrophic treatment is gene therapy. By introducing the gene sequences of neurotrophic factors to the cellular nucleus, the transfected cells may provide a sustainable endogenous production of neuroprotective substances.10,11 Via viral gene transfer, these factors were already implemented in the inner ear, although an expression of the introduced sequences did not demonstrate cell-specific gene transfer.12,13 Furthermore, only a temporary expression of about 3 weeks was achieved, which is not desirable in terms of long-term therapy.14 In addition, the use of viral vectors has considerable disadvantages, such as potential infection and the ability to trigger inflammatory or immunological processes.15 In addition to the viral vectors, artificially manufactured nanoparticles offer a promising ability to transport drugs and gene sequences with the ability of cargo release over a long period of time. Today, a variety of manufactured nanoparticles, which consist of organic and inorganic parts, can be assembled. In addition to their common uses in industry, a wide range of applications in health and medicine are achievable using nanoparticles.16 The advantages of nanoparticles are the impossibility of infection and the production of biodegradable scaffolds, for which a low response of the immune system is expected. Furthermore, nanoparticles can be produced inexpensively. By considering the property of the production of biological building principles, nanoparticles are ideal for the transport of medical drugs or genes. In addition to the transport function, it is possible to modify the surface of nanoparticles with specific receptors so that they will selectively bind to specific cells. The use of nanoparticles as a targeted treatment of specific cell populations results in a significant reduction of side effects.16 Recent research proved that fluoresceine-5-isothiocyanate (FITC)-labeled lipidic nanocapsules (LNC), locally inserted into the scala tympani of guinea pigs, infiltrated cell populations of the inner ear without causing functional or anatomical damage. 17 Those data were the first to demonstrate the ability of drug-unloaded LNC to enter inner ear cells. However, LNC-mediated drug delivery was not examined in that study. Besides the density of healthy SGC, the optimal effectiveness of cochlear implants is influenced by another important factor. In the postoperative onset of foreign body reaction, the organism encapsulates the implant through the production of fibrous tissue growth. This results in decreased nerve– electrode interaction, increased spread of neuronal excitation, reduced frequency selectivity, and increased impedances.18 Rolipram, an intracellular-acting phosphodiesterase-4 inhibitor, showed neuroprotective properties in former studies.19,20 Furthermore, anti-inflammatory effects have also been proven in animal models.21 We hypothesize that rolipram can potentially protect SGCs and reduce inflammatory reactions. If applied systemically, intravenously, or orally, rolipram has a bioavailability of 74%–77%.22 However, due to the blood–brain barrier, systemically-applied drugs that are used for inner ear treatment must be administered in such high dosages to have a biological effect on their target cells in the inner ear, that side effects may occur. To avoid massive side effects, local treatment of the inner ear is favored. In order to decrease the drugs applied locally to the inner ear, a targeted drug delivery is preferable. By encapsulating rolipram into a vehicle, such as LNC, a targeted drug delivery may be realized in the future. This will decrease the amount of drugs that are needed for human therapy. In the inner ear, a targeted drug delivery will lead to a significant dosage reduction and, as a result, to a lower risk of side effects when compared to systemic treatment. Additionally, the lower dose is also economically beneficial. We hypothesize that LNC provide a feasible drug-delivery system that can be used to transport rolipram into the cytoplasm. Once in the cytoplasm, rolipram will be released and induce its biological effects. This study examines the effect of rolipram and rolipram encapsulated in LNC on the survival rate, soma diameter, and neurite length of neonatally-harvested SGC in order to determine whether the drug’s effect is increased using LNC as a drug-delivery system. Furthermore, the effect of rolipram and the combination of LNC and rolipram is evaluated on the tumor necrosis factor-α (TNF-α) secretion of lipopolysaccharide (LPS)- stimulated dendritic cells (DC). This experiment indirectly provides information about the release of the payload and may demonstrate the potential of LNC as a delivery system for rolipram. Additionally, the results provide further insight into the anti-inflammatory effect of rolipram. This effect is due to the key role that TNF-α plays in the proinflammatory processes, which is appreciable in reducing postoperative reactions on cochlear implants. Based on in vitro results, we performed experiments on systemically deafened guinea pigs in order to examine LNC’s suitability for rolipram delivery in vivo.