In Chap. 2, we discussed the fundamental behavior behind the release of drug molecules from matrix species in response to degradation (i.e., chemical or enzymatic), erosion (i.e., surface or bulk), and swelling (i.e., crosslinks). In the case of swellable systems, we limited our focus only to the adjustment of swelling characteristics based on changing the crosslink density, polymer molecular weight between crosslinks, and hydrophilicity. These underlying features provide information regarding the pharmacokinetics of the system; however, they provide little indication of the physical requirements for actual therapeutic applications. For example, what if a swellable system reached a point within the human body where the matrix could not sustain its own structural integrity? What would be the consequences of the system breaking apart? Could we see premature drug release [1], an inflammatory response [2], or perhaps worse, the occlusion of an artery [3]? When we use swellable systems in physiological environments, care must be taken to understand the properties, both chemical and physical, to which it will be exposed throughout its life cycle within the body.In this chapter, we will discuss aqueous swellable systems classified as hydrogels [4], and their applications as implantable [5] and injectable [6] systems. Hydrogels are a species of crosslinked, hydrophilic, polymer molecules that absorb large amounts of water (≤99 %) to form a three-dimensional network. There is a broad application base for hydrogel materials, ranging from tissue engineering scaffolds [7] to breast implants [8] to contact lenses [9] (discussed in Chap. 2, Sect. 2.3). For the purposes of our current discussion, we will focus on implantable biosensors for diabetes treatment [10] and injectable hydrogels for cartilage repair [11]. We begin