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Cardiovascular tissue engineering strategies have been investigated in order to regenerate or repair scar tissue and/or hibernating myocardium following ischemic injury, in particular myocardial infarction (MI) (Pfeffer and Braunwald, 1990). Heart failure following MI continues to be a prevalent complication, in spite of current surgical revascularization techniques, due to the limited regenerative capacity of cardiac muscle (Sutton and Sharpe, 2000). Nanomaterials have been incorporated as critical components of experimental tissue engineering strategies for regeneration and repair of cardiac tissue (see Nguyen et al., 2015b). Nanomaterials can convey many benefits to cardiac tissue engineering and regeneration strategies including:

Metal NPs and carbon nanotubes (CNTs) can increase the conductivity of biomaterial scaffolds (Shin et al., 2013; Shevach et al., 2014; Zhou et al., 2014).

In this section, we will review some representative examples for the use of nanomaterials in cardiac regenerative therapeutic applications. Table 2 presents a summary of the main findings of the technologies discussed in this section and in Figure 2, we schematically depicted some of the technologies discussed in this review.

Iron oxide nanoparticles (IONP) occupy a special place in cardiovascular therapies as diagnosis agents; however, they have also recently sparked interest in the field of regenerative therapies for cardiac tissue by allowing the manipulation of cells containing IONP with an external applied magnetic force (Ito et al., 2005; Cheng et al., 2010; Souza et al., 2010). Several superparamagnetic IONP formulations (a.k.a. SPIO) (3–10 nm diameter) have been approved by the Food and Drug Administration agency (FDA) as magnetic resonance imaging (MRI) contrast agents for inflammatory diseases, as they are readily taken up by monocytes and macrophages following intravenous injection (Reimer and Balzer, 2003; Li et al., 2013). Pre-clinical and clinical studies have shown benefits of SPIO contrast agents in MRI-based detection of the infarct region post-MI (Yilmaz et al., 2012, 2013). The first application of SPIO in cardiovascular regenerative medicine therapies was to label exogenous stem cells in order track these cells after injection into the infarct region in rodent models of MI (Kraitchman et al., 2003). While several studies show that IONPs do not affect cell viability, phenotype or therapeutic potential (Au et al., 2009; Li et al., 2013), other studies have raised concerns on their safety (Mahmoudi et al., 2011, 2012; Ge et al., 2013). Furthermore, their ability to track transplanted cells by MRI is controversial as the uptake of IONP by resident macrophages in the advent of transplanted cell apoptosis results in false-positive signals of cell engraftment in the infarct (Amsalem et al., 2007). In addition to their use in imaging studies, super-paramagnetic iron particles were used to reduce acute wash out of transplanted cells from the infarct region in a rat MI model by iron labeling cardiosphere-derived cells (CDCs) in vitro and then applying a magnetic force over the infarct post-injection (Cheng et al., 2010). This magnetic targeting technique was able to increase retention of CDCs in the infarct region, which lead to improve cardiac function, reduced ventricular remodeling, and reduced infarct expansion post-MI (Cheng et al., 2010). In tissue engineering applications, magnetic force has been used to successfully manipulate IONP labeled cells in culture to create 3D tissue arrangements, including 3D small-diameter vascular grafts with three layers of cells containing IONP (endothelial, smooth muscle, and fibroblast cell layers) (Ito et al., 2005; Souza et al., 2010). A novel application of IONP by (Han et al., 2015) was to enhance the cardiac lineage differentiation of mesenchymal stem cells (MSCs) prior to delivery to the infarct region post-MI in an effort to enhance cardiomyocytes regeneration. It was proposed that IONP triggered an intracellular signaling cascade, which enabled gap junctional coupling of IONP-cardiomyocytes with MSCs, and further activated cross-talk between cells. In this study, a co-culture system of MSCs with IONP-cardiomyoblasts was employed and the presence of IONP effectively increased cardiomyocyte (CM) markers, gap junctions, and pro-angiogenic cytokine expression in MSCs (Han et al., 2015). These primed MSCs were easily separated from the IONP-cardiomyoblasts via magnetic-activated cell sorting and had significantly greater therapeutic efficacy in a mouse MI model, in terms of preserved cardiac function, lower fibrosis, infarct scar area, and survival 2 weeks post-MI compared to unprimed MSCs (Han et al., 2015).

Gold nanoparticles (AuNPs) and gold nanorods (AuNRs) have been investigated in biomaterial scaffolds to boost conductivity in an effort to improve propagation of electrical signals through an engineered cardiac tissue, which will ultimately enhance in vivo integration. AuNRs were incorporated into alginate hydrogels to improve the electrical conductivity of the material and aid in the coupling of cardiomyocytes seeded within the scaffolds (Dvir et al., 2011). The incorporation of the nanorods (NRs) improved the connection and alignment of seeded cardiac cells (cardiomyocytes and fibroblasts), and increased gap junction proteins and expression of proteins involved in contraction and electrical conductivity (Dvir et al., 2011). AuNPs have been incorporated into decellularized omentum tissue scaffolds to decrease scaffold electrical resistance with the goal to produce autologous cardiac patches (Shevach et al., 2014). The incorporation of neonatal cardiac cells into these AuNP-conjugated scaffolds reduced the threshold required for contraction compared to the biomaterial alone, which was accompanied by greater gap junction protein expression, striation formation similar to cardiac muscle, and velocity of calcium of transients in response to electrical stimulation (Shevach et al., 2014). AuNPs have also been incorporated into thermo-responsive hydrogels of collagen nanofibers (Orza et al., 2011) and chitosan polymer (Baei et al., 2016) with the objective of forming injectable formulations for minimally invasive delivery of cells to the infarct. In the study by Orza et al., MSCs cultured AuNP-coated collagen fibers exhibited faster cardiac lineage differentiation after exposure to cardiac differentiation medium as compared to standard tissue culture substrate. Similarly, AuNPs enhanced the expression of cardiac lineage markers in MSCs cultured in chitosan hydrogels along with improving the conductivity of the material (Baei et al., 2016). Furthermore, AuNPs have shown antifibrogenic activity in vitro, by decreasing the percentage of fibroblasts with activated myofibroblast phenotype (Sisco et al., 2008). However, in spite of these advances in AuNPs scaffold development, no in vivo data are available to confirm a benefit of incorporating AuNPs into tissue-engineered scaffold on cardiac function post-MI in animal models. These in vivo studies will be necessary to determine if the injectable scaffold or cardiac patch can effectively propagate electrical signals in vivo without interfering with the directional signal propagation and cardiac contraction, which could produce arrhythmias.

The toxicity of AuNPs in vivo is controlled by many factors including: size, capping agents, and dosage (Khlebtsov and Dykman, 2011). A preliminary study by Spivak et al. indicated that spherical AuNPs of 30-nm diameter (3.19 g/mL metal concentration) could be intrapleurally delivered, which exhibited reduction in hydrothorax incidence and fibrosis in a doxorubicin induced rat model of heart failure similar to that of inotropic agent Simdax (Spivak et al., 2013). No appreciable toxicity due to AuNPs was noted over 6 months. Finally, another in vivo application of AuNPs was to improve the mechanical properties of porcine aorta decellularized vascular grafts by crosslinking them to mercaptoethylamine functionalized spherical AuNPs (100 nm) (Ostdiek et al., 2015). The grafts were able to integrate into the aortic tissue in a pig model, with cellular infiltration into the graft, without signs of inflammation or stenosis.

Nanomaterial allotropes of carbon, in particular CNTs and graphene oxide (GO) sheets, have received interest in the design of tissue engineering strategies to regenerate functional myocardium following infarction due to their high conductivity. CNTs have been investigated in vitro by Shin et al. who incorporated CNTs into a gelatin methylacrylate (GelMA) cross-linked hydrogel (Shin et al., 2013). The authors observed that CNTs provided electrical connections, similar to native Purkinje fibers in the heart and allowed conduction in a material that previously was an insulator (Shin et al., 2013). In addition, CM retention, viability, expression of contractile proteins, established striations, and functional gap junctions were enhanced on the scaffolds containing CNTs as compared to hydrogels alone. Furthermore, hydrogels containing CNTs were used as a substrate for the growth of 3D artificial tissues that exhibit beating under pulsatile stimulation (Shin et al., 2013). CNTs have also been investigated as a growth substrate, as they exhibit a topography similar to the native ECM with the ability to relay signals between myocytes (Martinelli et al., 2012). Cardiomyocytes grown on CNT substrates had increased viability, entrance into the cell cycle, and more negative resting membrane potential as compared to standard culture conditions (Martinelli et al., 2012). In vivo evidence in mice indicated that therapeutically relevant concentrations of CNTs are non-toxic; thus, there is promise for further in vivo studies with this nanomaterial (Schipper et al., 2008). Lastly, an engineered cardiac tissue consisting of neonatal rat cardiac cells in a gelatin hydrogel with single-walled CNTs (SWNTs) allowed spontaneous contraction and action potentials in vitro in addition to maturation of cardiomyocytes (Zhou et al., 2014). After suturing the graft onto the infarct region in a rat model, with immunosuppression therapy, improved cardiac function 4 weeks post-application and increase in gap junction protein expression was observed (Zhou et al., 2014). It is noted in this study that there was local macrophage upregulation in SWNT-graft treated mice leading to incorporation of SWNTs into the infarct region. As this study is performed with immunosuppression therapy, further investigation of long-term effects of CNTs in vivo, in particular the activation of an immune response in model with healthy immune function, is still needed.

Graphene oxide (GO) sheets are an alternative carbon-based nanomaterial, which have shown biocompatibility with no acute toxic effects in vivo (Paul et al., 2014; Park et al., 2015b). GO sheets and flakes with a thickness on the nanometer scale and length in the area of 1–6 μm are not taken up by cells but can absorb ECM proteins from culture serum (Lee et al., 2011). Studies by Park et al. demonstrated the benefit of incorporating GO or reduced GO flakes into MSC culture, with the following observations: (1) GO adsorbed ECM components (fibronectin) from the serum and formed GO-cell and cell-ECM interactions, which activate both pro-survival pathways and pro-angiogenic cytokine secretion and (2) the conductivity of GO stimulated expression of cardiac specific makers and gap junctions (Park et al., 2015b). The result in vivo in a rodent MI model showed enhanced retention of the MSC + GO in the infarct, reduced sensitivity to oxidative stress following ischemia reperfusion injury, and improvement of heart function by cellular cardiomyoplasty without an immune response to the GO material (Park et al., 2015a). Furthermore, polyehtylenimine functionalized GO sheets have been investigated as a transfection agent for gene therapy approaches to enhance angiogenic vascular endothelial growth factor (VEGF) gene expression using an injectable GelMA hydrogel (Paul et al., 2014). In a rat MI model, delivery of the composite GO-VEGF hydrogel lead to increased capillary density and decreased infract scar size (Paul et al., 2014). Injectable hydrogel formulations containing GO tethered VEGF plasmid were, therefore, an effective transfection system to enhance VEGF expression in the infarct region. Cerium oxide NPs act as free radical scavengers and have been shown to reduce pro-inflammatory cytokine expression due to reduction of endoplasmic reticulum (ER) activated reactive oxygen species (ROS) in a murine model of heart failure (Niu et al., 2007). The NPs improved heart function and limited ischemic remodeling. These results have been replicated in in vitro systems, including cardiomyocytes exposed to cigarette smoke extract and cardiac progenitor cells in culture in which CeO₂ enhanced survival and maintenance of multi-lineage differentiation (Niu et al., 2007; Pagliari et al., 2012).

Injectable biomaterials composed of hydrated natural or synthetic polymers solutions have been used as therapy for treating hearts post-MI (Christman and Lee, 2006). These hydrogels can limit wall stress that leads to pathological dilative remodeling of the ventricle as well as provide a protective environment to improve retention and function of transplanted cells (Johnson and Christman, 2013). Another ECM therapy approach is the fabrication of nanofiber matrices (Zhang, 2003). Nanofiber diameter can be controlled so that it is to scale with that of native ECM fibers and can offer greater surface area for cell engraftment (Mukherjee et al., 2011). Several nanofiber meshes made from synthetic polymers functionalized with native ECM proteins have shown in vitro the ability to produce scaffolds with similar topology to heart tissue, with aligned rabbit cardiomyocytes that express mature CM contractile protein and gap junction markers as compared to traditional culture techniques (Kai et al., 2011). Furthermore, nanofibers have been implemented in vascular grafts to provide a bioadsorbable scaffold and allow for neo-arteriogenesis and improved long-term graft patency (Pektok et al., 2008; Wu et al., 2012).

Peptide nanofiber injectable hydrogels have been used successfully for both cell and growth factor (GF) delivery in promoting regeneration post-MI (Hynesl et al., 1995). Table 3 summarizes some studies that have shown increased cardiac function post-MI when using peptide nanofiber-based tissue regeneration strategies. Nanofibers are formed by the self-assembly of short oligopeptides, with alternating hydrophilic and hydrophobic amino acid residues, when they introduced to neutral pH and osmolality (Zhang, 2003). Seminal in vivo studies by Davis et al., 2005, indicated that the porous hydrogel material from RAD16-II peptides (AcN-RARADADARARADADA-NH2) could be injected into the healthy myocardium without eliciting an immune response. This material was biodegradable and provided a microenvironment that recruited endothelial, smooth muscle and myocyte precursor cells (Davis et al., 2005). In MI animal models, peptide nanofibers, made from RAD16-II, have shown the capacity to increase exogenous cell retention in the infarct and facilitate the controlled release of GFs to prevent CM apoptosis or recruit endogenous precursor cells; all with the outcome of improving cardiac function (Davis et al., 2006). Furthermore, a study by Lin et al. concluded that in a porcine model the peptide nanofiber scaffold was not only a passive delivery vehicle but also improved diastolic function post-MI through reduction of fibrosis, neo-capillary formation and reduced ventricular remodeling (Lin et al., 2010). Similar studies in small animal models showed positive, yet non-significant, effects of nanofibers alone; however, combined with the incorporation of GFs or endogenous stem cell recruitment factors significantly improved cardiac function was achieved (Davis et al., 2006; Lin et al., 2012). Peptide nanofiber-based scaffolds represent a bottom-up approach to fiber formation where small, chemically synthesized oligopeptides are the building blocks. A benefit of this approach is that the peptide building block sequence can be customized to the needs of the application, as seen in a study by Ban et al. in which amphiphilic peptides were synthesized with a matrix metalloproteinase-2 (MMP2) and integrin binding cell adhesion sequence to replicate native cues for CM attachment prior to material injection (Ban et al., 2014). Further work has aimed to enhance the angiogenic capacity of self-assembling peptides. Kumar et al., for instance, developed a peptide sequence that incorporates a VEGF-165 mimicking peptide that enhanced angiogenesis in vivo without the need for delivery of exogenous GFs (Kumar et al., 2015). A drawback for many of these studies is that material injection must occur directly into the myocardium via an open chest procedure as the material gels instantly once exposed to native pH and osmolarity. Thus, to allow non-invasive delivery, Nguyen et al. designed brush peptide polymer amphiphilic NPs with an MMP degradable peptide sequence. These NPs can be injected intravenously, accumulate through leaky vasculature in the infarct region and due to inflammatory protease activity, transition into a gel that is retained in the infarct (Nguyen et al., 2015a).

In the future, nanomaterials for cardiac regeneration will continue to provide a novel opportunity to enhance the conductivity of biomaterial scaffolds but will require in vivo testing in small and large animal models to test for the possibility of arrhythmias. The development of nanofiber matrices has provided a bottom-up approach to create an ECM-mimicking environment to control cell growth and differentiation. Nanofiber scaffolds as biodegradable vascular grafts could reduce the advent of restenosis and promote regeneration. Nanomaterials, in particular noble metal NPs, are increasingly becoming key components in tissue-engineered materials for cardiac and vascular regeneration in patients with MI, heart failure or coronary artery disease.

Diabetic foot infections (DFI) are part of the pathological profile of diabetic foot ulcers (DFU), where factors, such as arterial insufficiency and immunological disturbances, contribute to their chronic nature (O’Loughlin et al., 2010; Andrews et al., 2015). Statistics point to the fact that DFU and DFI are the major underlying causes for hospitalization and lower limb amputation (Uckay et al., 2015). The current guidelines for treating DFI include systematic antimicrobial therapy, which often does not work in moderate to severe cases (Lipsky et al., 2012; Uckay et al., 2015). This is combined with surgical procedures (Pinney et al., 2002; Mueller et al., 2003; Greenhagen et al., 2012; Colen et al., 2013; Cychosz et al., 2015), or revascularization, in combination with non-surgical wound care therapies, such as custom shoes and orthotics, which to this day remains unclear if they actually prevent the onset of DFU (Cychosz et al., 2015).

Wound healing is a complex biological process that involves inflammation, chemotaxis, angiogenesis, and tissue remodeling (Singer and Clark, 1999; Baum and Arpey, 2005; Gurtner et al., 2008). Chronic wounds are defined as lesions that present impaired (i.e., slow) wound healing (Kirsner and Eaglstein, 1993). Among possible causes for such impaired healing is the persistent inflammation within the actual wound, caused by bacteria colonization, for example (Ehrlich, 1998; Fukai et al., 2005), which is exacerbated in diabetic patients (Lookingbill et al., 1978; Madsen et al., 1996; Robson, 1997; Sibbald et al., 2000; Baltzis et al., 2014; Eming et al., 2014). This permanent inflammatory state results in early degradation of newly forming tissue, creating a never-ending loop of wound healing (Rogers et al., 1995; Yager et al., 1996; Kahari and Saarialho-Kere, 1997; Trengove et al., 1999; Liu et al., 2009). Furthermore, this scenario gets even more complex in the presence of bacteria capable of forming biofilms in diabetic foot wounds such as Pseudomonas aeruginosa (Uckay et al., 2015) and multidrug-resistant Staphylococcus aureus (Banu et al., 2015).

An assessment of the extent of DFU by a wound care expert is followed by debridement, and sequential revaluation of the wound site for surgical reconstruction. Particularly, soft tissue reconstruction can be as simple as letting the wound heal by itself, a.k.a. secondary intention, or healing assisted by microsurgical flaps. The use of skin substitutes (cadaver skin, xenografts, and artificial substitutes) has exponentially improved in quality and regenerative capacity. They offer, in most cases, a temporary solution, especially for large wounds with truncated geometries. Autologous grafting and/or flap transplantation also present some drawbacks since they require mechanical harvesting of donor skin, which causes morbidities, such as pain, risk of infection, discoloration, and scarring. Furthermore, most autologous grafts use only the epidermal coverage of the skin, which together with leaving a scarred donor site, does not provide a completely functional barrier to the wound (Tam et al., 2013).

Thus, over the past few decades, there has been a rise of the so-called biocompatible healing products intended for skin regeneration in the form of skin grafts and wound dressings (O’Loughlin et al., 2010). Amniotic membranes appear promising candidates; however, the risk of infection, as well as their limited availability, makes their use unrealistic as a viable definitive treatment for DFU (Zelen et al., 2013; Lavery et al., 2014; Cychosz et al., 2015). Thus, lab-made living-tissue-engineered products, which were originally designed to act as skin grafts, are now also being employed for filling of DFU, where the ECM of the engineered material promotes an angiogenic response within the wound, which in turn accelerates wound healing (Veves et al., 2001; O’Loughlin et al., 2010). Apligraf^® (Novartis, Organogenesis, Inc.) and Dermagraft^® (Advanced Biohealing, Inc.) are two of the most popular products for treating skin wounds, including DFU, in North America (Veves et al., 2001; Marston et al., 2003; O’Loughlin et al., 2010). Both are contraindicated in wounds with signs of infection. In addition, they are recommended for limbs with good blood supply, and in some cases several applications of the scaffold are required (Veves et al., 2001; Marston et al., 2003; O’Loughlin et al., 2010; Holmes et al., 2013). Other therapies, such as hyperbaric oxygen and negative pressure, have emerged also as potential non-surgical alternatives for treating DFU; however, clinical evidence does not fully support their use (Londahl et al., 2010; Dumville et al., 2013; Ma et al., 2013; Rhee et al., 2014; Cychosz et al., 2015).

Full-skin functional substitutes remain an elusive problem for skin tissue engineering in burn units. Depending on the burn degree and extent, the surgeon could decide on using split thickness autograft from the patient, which will result in non-functional transplanted tissue (missing sweat glands) (Tam et al., 2013). This treatment is only suitable when there are enough healthy donor sites in the patient. Thus, as similar to the above discussed for DFUs, laboratory engineered materials had been developed to fulfill the need for alternative strategies for wound covering and tissue regeneration in these patients (Ulrich, 2014). Furthermore, the control/prevention of nosocomial infections in burn patients is a pivotal factor for reducing hospital stays and morbidity (Norbury et al., 2016).

In the following sections, we will highlight the progress made regarding nanomaterial use for skin regeneration. Table 4 summarizes some representative examples of hybrid/composites that were tested in vivo for dermal skin tissue regeneration. Figure 3 displays a representative summary of the technologies presented herein.

The outstanding advancements in nanomaterial therapies for skin regeneration are bringing us closer to the availability of new multi-functional materials that provide multiple wound-healing properties. For example, the incorporation of stable nanosilver to provide anti-inflammatory and antimicrobial properties to any given template presents an interesting and appealing strategy. However, better understanding on the nanoscale interactions between biopolymers and nanomaterials is required to allow de novo engineering of tissue scaffolds for tissue engineering.

The cornea is a transparent layer on the anterior surface of the eye, which overlaps the anterior chamber. In addition to the cornea, the iris, pupil, and lens focus light onto the pigmented interior layer. The human cornea mainly comprises many collagen layers organized to ensure full clarity of light. Furthermore, there are no blood vessels on the corneal epithelial in support of its transparency. However, it is vulnerable to many physical and environmental dangers due to its forefront position. A prominent issue is found with dry eye disease, which directly interferes with corneal function due to tear film imbalances and surface inflammation. Direct damage to the cornea, minor or significant, can have a tremendous effect on vision; thus, a leading cause of blindness, affecting ≈4.9 million individuals who are bilaterally blind, and another ≈ 23 million who are unilaterally blinds (Oliva et al., 2012). The surgical replacement of the damaged cornea by transplantation from a cadaveric donor remains as the gold standard treatment. The severe shortage of donors in most countries, particularly in developing countries, has motivated the search/research for man-made corneal substitutes. Currently, refractive eye surgeries and synthetic corneal replacements (keratoprostheses) are applied to combat this issue but are limited in several ways. Primarily, post-operative complications, such as infection, are rampant for many patients (Griffith et al., 2012). Furthermore, synthetics are incompatible at times depending on the individual and are at risk of biological rejection and induction of further ocular problems (Griffith et al., 2012).

Biocompatible and bioactive nanomaterials can possibly minimize complications associated with corneal regeneration. Intrastromal injection of peptide amphiphile (PA) nanofiber scaffolds modified with YIGSR (fibronectin peptide) or RGD (laminin peptide) sequences, into rabbit cornea were applied for corneal wound healing. Analysis after 3 and 7 weeks post-injection with RGD displayed significant migration of stromal keratinocytes and enhanced regeneration of the damaged cornea (Uzunalli et al., 2014). Furthermore, the opacity of the cornea was unaffected by the treatment. Also, the incorporation of nanosilver into collagen hydrogels can produce collagen mimetic matrices with antimicrobial properties (Alarcon et al., 2016).

Sometimes point-specific corneal healing is insufficient and replacement is necessary. As appealing as natural scaffolds are for replacement, the structural limitations associated with the size of the material (prone to degradation and fracture) remain a problem. Furthermore, the replacement must ensure full compatibility with the surrounding tissues (nerve and muscle) with acceptable refractive transparency. Fagerholm et al. performed a phase I trial of corneal replacement treatment using biosynthetic recombinant human collagen (rHC) type III. This 10% (w/w) rHC type III is EDC/NHS cross-linked within an appropriately sized corneal mold. The assessment over a 2-year period reported no signs of transplant rejection, infection, or immunological reaction. Visual acuity among patients was similar to normal cornea function across the study (Fagerholm et al., 2010). Furthermore, sufficient nerve regeneration and stromal repopulation was found in patients over a 4-year period following the original study (Fagerholm et al., 2014). The long-term safety and efficacy denoted in these studies is promising for future applications.

NP structures, such as liposomes, can also improve the effectiveness of antimicrobial drugs (Chaurasia et al., 2015). Furthermore, NPs and NP structures are excellent drug and gene carriers that can promote site-specific delivery and bioavailability to corneal epithelium (Attama et al., 2009; Sharma et al., 2011). In addition, metal NPs integrated on surface scaffolds are highly effective antimicrobial agents that can reduce post-operative complications (Santoro et al., 2007). Scaffolds made of natural (chitosan) and synthetic (PCL) components are well received in eye transplants for ocular inflammation treatment (Zarbin et al., 2013).

The retina is an expansive neural network, consisting of two layers: a pigmented layer for light absorption and a neural layer dense with photoreceptors. The retinal layers are vital for sensory integration, feedback, and processing of all visual information via chemical and electrical signals. This information is guided by the optic nerve to the brain. Retinal complications are very serious and often are associated with AMD and glaucoma. In addition, genetic abnormalities in photoreceptor function, pigmented cells, and ganglion density can contribute to congenital blindness. A major challenge with current therapies is penetrance of the blood–retina barrier and site-specific distribution of bioactive agents.

Neovascularization of the subretinal space leads to loss of visual acuity. This is treated with continuous intravitreal injections of inhibitors (anti-VEGF) to minimize vascular expansion and thus improve vision. However, the injections are quite costly and invasive. Also many patients experience minimal recovery or vision loss continues to diminish. In a study by Luo et al. (2013), a single injection of RGD-coated PGLA NPs with Flt23k (anti-VEGF plasmid) transcripts was applied to an AMD primate and choroidal neovascularization (CND) murine model. This systemic intravenous injection minimized the administration risk and the NP solution was biocompatible in both animal models. It was found that ~86% of mice displayed a 12.2 ± 5.2% improvement to visual acuity (Luo et al., 2013). Furthermore, CND and fibrotic scar volumes were reduced in both animal models (Luo et al., 2013). In another study, bare titanium dioxide (TiO₂) NPs were injected into mice with oxygen-induced retinopathy (Jo et al., 2014). Interestingly, the TiO₂ NPs had a low toxicity profile in the trial with signs of reduced retinal neovascularization. There are many proposed nanomaterial scaffolds and drug-carriers that are protective and regenerative for retinal photoreceptors and neurons (Zarbin et al., 2013; Lin et al., 2015; Varshochian et al., 2015).

Degeneration associated with AMD is one of the major causes of blindness in the world. Dry AMD is characterized by gradual loss of vision as drusen accumulates between retinal pigment epithelial and Bruch’s membrane (Cai and McGinnis, 2016). There are many factors associated with this progression, including biochemical and molecular mechanisms. Most therapeutic methods focus on inflammatory pathways or cell-based rejuvenation of tissue. Cerium oxide NPs (CeNPs), commonly known as nanoceria, have antioxidant catalytic activity similar to endogenous defense enzymes. In a study by Kong et al., low-dose nanoceria was systemically injected into mice with retinal defects to observe retinal function and the effects on ROS levels. The nanoceria reduced concentration of ROS in the subretinal space, and preserved photoreceptor integrity by the upregulation of pro-survival genes and downregulation of apoptotic signals (Kong et al., 2011). This work has been assessed in different injury models, including the latest example by Wong et al. (2015). Single-dose CeNPs catalytic activity was consistent over a 7-day period, with a decline by day 14, which was able to prevent photoreceptor degradation in a retinal degeneration rodent model (Wong et al., 2015).

The advances in ophthalmological nanomedicine are staggering, and few challenges seem to remain before the advent of major innovations. The application of biocompatible, biofunctional materials for corneal regeneration or replacement holds great promise. As described, corneal fibrotic scarring and neovascularization are reversible using various methods, or combinations, of nanomaterials, metal NPs, or nanoparticulate structures. A major advantage provided by noble metal or polymeric NPs, dendrimers, and liposomal nanotechnologies is mobility across the blood retina barrier, allowing for accumulation and sustained bioactivity or release of anti-inflammatory and antivascular drugs (Chaurasia et al., 2015; Jo et al., 2015). In addition, the composition and size of NPs elicit minimal immunological reaction. Ocular therapeutics is more manageable compared to other organ/tissue targets, specifically in terms of administration, cost/utility of materials, and structural penetrance and localization. However, the benefits attributed to ocular nanotechnologies are not without its flaws. Beyond improving therapeutic outcomes, further long-term assessment of NPs distribution and eventual clearance is required to fully evaluate toxicity, bioavailability, and stability (Chaurasia et al., 2015). Nanoemulsions and cell-based therapies for ocular diseases are prime candidates for clinical phase trials (Ramsden et al., 2013; Chaurasia et al., 2015). Nonetheless, it is expected that ocular nanomedicine will cause a shift in translational practices (Etheridge et al., 2013). The number of viable, novel therapeutics will expand considerably following further elucidation of nanomaterial regenerative mechanisms. Furthermore, the technological advances in design tools and integrated nanomaterial components will match this movement. This will guide approaches into a clinical perspective, such as hybrid diagnostic/therapeutic systems, targeted drug systems, and quite possibly gene delivery.

Skeletal muscles are responsible for the majority of the active movements in the body that keep everyone in motion. The SMs are organized as bundled (fascicles), layered muscle fibers (myofibers) integrated with connective tissues, nerves, and blood vessels (Grasman et al., 2015). Contraction of these muscles requires substantial energy, and the SM plays a structural (support soft tissues, posture) and functional (temperature regulation, skeletal movement) role in the body. SM hypertrophy is essential to growth/development and lifelong fitness; and these tissues regularly undergo regeneration (Grasman et al., 2015; Wolf et al., 2015). However, recovery from medical problems dictated by atrophy, nerve dysfunction or significant volumetric muscle loss (VML) is limited and typically results in irreversible scar formation (Grasman et al., 2015; Wolf et al., 2015). The application of nanomaterials in tissue engineering is expected to fulfill many niches in SM tissue regeneration and restoration. Key characteristics necessary for the translation of novel materials include: biocompatibility, biodegradability, conductivity, and promotion of cell alignment, vascularization, and innervation. The physical and chemical features of nanomaterials determine functionality, which is often modulated by the addition of GFs, pharmacological drugs, and NPs. The following sections will cover the current nanomaterial progress and challenges in SM tissue regeneration with a focus on in vivo application. Table 6 summarizes the main findings for the literature presented in this section.

Nanomaterials intended for SM tissue regeneration are often categorized as natural or synthetic scaffolds. Currently, significant interest is placed on novel hybrid/composite scaffolds implementing the best features of both types. Natural-based scaffolds comprise essential ECM proteins, such as collagen, fibrin, and hyaluronic acid or decellularized tissue complexes (Wolf et al., 2015). The ECM maintains healthy organ function; thus, scaffolds of this origin are biocompatible, biodegradable, and bioactive for regenerative uses (Kin et al., 2007; Klumpp et al., 2010; Sicari et al., 2014). Furthermore, the inherent nature of these materials can enhance cell-based therapies. However, preparation inconsistencies and material degradation (Koning et al., 2009; Sicari et al., 2014) are frequent issues, in addition to human translational limitations for animal-based natural scaffolds. These materials are manufactured primarily as 2-D sheets from their natural constitutes, designed for external applications. In addition, hydrogel soft materials can develop unique 3D shapes that can be further manipulated with cross-linkers or non-covalent bonding. In a study on in situ muscle regeneration, Ju et al. observed Pax7-positive cells (SCs) infiltrate gelatin-based scaffold implanted in the tibias anterior (TA) of mice (Ju et al., 2014). Myogenic-inducing factors (SDF-1α, HGF, IGF-1, bFGF) were added to separate scaffolds during production. The release of myogenic factors facilitated cell accumulation. In particular, IGF-1 scaffolds showed significant fiber growth, prompted by myogenic differentiation of infiltrated cells, after a 2-week implantation (Ju et al., 2014).

Synthetic scaffolds are reputable for their customization of physical and chemical features and ease of manufacturing process. Nonetheless, these materials are often toxic to cells in vitro and require modifications (coatings, surface proteins) to promote biocompatibility (Grasman et al., 2015; Wolf et al., 2015). Common examples include poly(lactic acid) (PLA), PEG, and poly(ϵ-caprolactone) (PCL). The choice of material determines the capacity of its function, yet difficulties are found in all types for promoting long-term vascularization and myofiber growth (Grasman et al., 2015; Wolf et al., 2015). The production control over synthetic materials allows for an array of configurations. Meshes are designed to maximize surface area and provide incredible structural support. Foams and hydrogels are highly porous, elastic materials capable of interior storage and in situ polymerization. Fiber-based scaffolds are thin, interwoven sheets fabricated typically by electrospinning methods. Fiber length, thickness, and alignment can be predetermined by set electrospinning parameters that allow for abundant choice in design (Grasman et al., 2015; Wolf et al., 2015). Nanofibrous scaffolds can mimic macromolecular sizes to enhance material–ECM interactions (Grasman et al., 2015; Wolf et al., 2015). Furthermore, fiber orientation can promote myoblast adherence and proliferation (Chen et al., 2013). A novel approach in coaxial electrospun scaffolds explored by McKeon-Fischer et al. involves two-layered fibers that induce movement similar to muscle myofibers. The inner core of the fibers comprises PCL and conductive multi-walled carbon nanotubes (MWCNT) and the outside is coated with polyacrylic acid (PAA)/polyvinyl alcohol (PVA) hydrogel that act as an ionic polymer gel (IPG). Following the implantation of these scaffolds into injured vastus lateralis (VL) muscle, myogenic growth was observed at the site (McKeon-Fischer et al., 2014).

Composite scaffolds integrating natural/synthetic properties are showing promise for SM tissue regeneration. These materials are developed with a combination of the individual methods discussed above, usually represented by dual-layered fiber scaffolds or interior/exterior interplay. ECM-derived surface coatings can minimize the foreign body reaction by synthetics. In addition, incorporated PEG or PCL polymers enhance mechanical durability for degradable natural polymers. An electrospun PCL/collagen composite scaffold, seeded with human SM cells, was biocompatible and promoted cellular adhesion and proliferation. In addition, the orientation of scaffold fibers influenced the alignment of muscle cells and facilitated myotube formation (Choi et al., 2008a). As a follow-up, Zhao et al. used the same PCL/collagen scaffold implanted in vivo to resolve diaphragm defective mice over a 6 months period. The material promoted cell migration and adhesion, showing alignment and subsequent tissue formation within and around the scaffold. Physical characteristics of the material matched normal diaphragm tissue, and the implant did not invoke a host response or herniation (Zhao et al., 2013). A PEG-fibrinogen (PF) hydrogel scaffold, with young or aged muscle-derived pericytes, was found to improve myogenic differentiation and angiogenesis (Fuoco et al., 2014). Furthermore, aged pericytes seeded on the scaffold had rejuvenated function that matched young pericytes. This transformation is influenced by the features of the scaffold, which mimic ECM mechanical and functional properties (Fuoco et al., 2014). The capability for hybrid/composite scaffolds to specifically match certain applications by varying a number of parameters on the natural and synthetic components allows for a greater improvement against the challenges of SM regeneration.

There is a relatively expansive outlook on the role NPs can play in SM tissue regeneration. However, the majority of studies are confined to physical/chemical characteristic assessments and in vitro display of biocompatibility, release-kinetics, and cellular functional response. Nonetheless, progress is apparent as our understanding of the structural and functional features these NPs contribute is elucidated. NPs are frequently used as imaging agents (Fang and Zhang, 2009; Adriana et al., 2015) and carriers for GFs or drugs (Arvizo et al., 2012), though this has been limited so far for SM tissue applications. Bibee et al. developed rapamycin-loaded perfluorocarbon NPs that increased physical performance, specifically forelimb grip strength, of both young and old mice. The NPs accumulated at sites of inflammation, where rapamycin induced autophagy that promoted muscle recovery (Bibee et al., 2014). The concentration of drug within NPs, injected via the lateral tail vein, required for this effect is 10 times less than is required with oral supplementation. This is an example where nano-therapeutics can replace existing treatments (corticosteroids, physical therapy) or offer a novel means to promote recovery at a biochemical and molecular level.

Notably, noble metal NPs impart electrical conductive and catalytic functions useful for enhancing nanomaterial effectiveness (Arvizo et al., 2012). However, conductive properties particular to noble metals in SM scaffolds are rarely applied, though the use of multi-walled CNTs has been successful (Quigley et al., 2012; McKeon-Fischer et al., 2014). Parameter changes in pre- and post-production readily alters physical characteristics, such as size, shape, and composition (Arvizo et al., 2012). Metal NPs are usually produced via chemical reduction, followed by downstream purification processes (Arvizo et al., 2012). An area continuously under study is the compatibility of metal NPs in specific tissues, which is heavily focused on NPs concentration and distribution. McKeon-Fischer and Freeman developed electrospun PLLA-AuNPs composite scaffolds with three varying concentrations of AuNPs (7, 13, and 21%) to enhance the healing process (McKeon-Fischer and Freeman, 2011). The proliferation of cells was minimal, yet interestingly the lowest concentration of AuNPs conferred relatively similar results compared to the higher concentration variants. Structural integrity was stable over 4 weeks and the AuNPs did not show signs of toxicity. In regard to coating, metal NPs are capable of promoting cellular interactions and maintaining cell presence at the scaffold surface, which enhances their functional ability (Ishizaki et al., 2011).

The majority of studies on SM regeneration focus on physical injury and loss of SM tissue; however, it may be beneficial to aim at biochemical and molecular dysfunction as well. The role of AuNPs in oxidative stress for exercised-induced muscle damage was evaluated in rats over a 21-day period. Inflammation is active in the presence of ROS, which contributes to SM damage. Phonophoresis (ultrasound-guided delivery) of AuNPs was found to reduce inflammation, denoted by a decrease in many pro-inflammatory markers and oxidative stress markers (superoxide and NO), and an increase in total glutathione levels (Zortea et al., 2015). In addition, it was found that a gold embedded, decellularized porcine diaphragm scaffold promoted fibroblast proliferation and attachment, yet high Au concentration increased free radical levels (Cozad et al., 2011). It would be interesting to see a follow-up involving AuNPs release from hybrid/composite scaffolds for in vivo SM regeneration.

It seems that NPs in SM regenerative applications are in the early stages of development in terms of their potential. The coming years will show how valuable metal NPs features are to modulating scaffold functions and influencing physical/chemical characteristics when based on their extensive foundational study.

Key functional effects prioritized in recent SM regeneration studies include cell migration into/onto nanomaterials, alignment of neighboring cells or newly proliferative cells, and electrical stimulation of scaffolds. Furthermore, elucidation of material–cell–tissue interactions in vivo is vital for facilitating the transition from proof-of-concept design to pre-clinical or FDA-phase trials (Grasman et al., 2015; Wolf et al., 2015). Currently, an incredible variety of nanomaterials are available, yet few boast truly significant in vivo compatibility and regeneration in long-term studies. In part, this is due to limitations in the animal models for SM regeneration. Popular methods of injury include laceration, ischemia, and weighted-trauma. If the induced injury is minimally disruptive, normal SM regeneration takes precedence over potential effects from scaffolds. Furthermore, if the basal membrane remains after injury it can act as a template for satellite cell migration (Wolf et al., 2015). By contrast, VML injuries remove considerable muscle tissue but consistency is difficult to maintain across animal models and injury site (Grasman et al., 2015). Sometimes toxins are introduced to permanently limit SM function. It will be important to fully describe such methods in practice for studies aimed at translational applications.

Skeletal muscle regeneration is a multifaceted endeavor. In order to meet this demand, substantial tissue replacement/healing must be induced by facilitated proliferation and differentiation of neighboring SM cells. Furthermore, promotion of axonal growth and innervation will improve communication with damaged peripheral nerves. In addition to SM regeneration, it will be necessary for nanomaterials to promote both angiogenesis and neurogenesis. Noble metal NPs show promise; however, steps need to be taken to elaborate on their effects in vivo. This advancement will likely involve hybrid/composite materials associated with metal NPs and progenitor cell delivery.

The nervous system is essential to the functional relay and processing of information outside and within the human body. It is categorized by two divisions: the CNS, which includes the brain and spinal cord, and the peripheral nervous system (PNS) that comprises all other neural tissue in the body (Goldberg and Barres, 2000). The basic neural unit, the neuron, is capable of receiving and sending signals at rapid speeds. The CNS integrates, processes, and coordinates sensory and motor information to enable a functional response. The PNS primarily sends signals to the CNS, via the spinal cord, and delivers signals to other cells within the body (Goldberg and Barres, 2000). However, the nervous system is susceptible to acute or chronic damage alike to the other tissues in the body. People of all ages suffer from neural complications, induced by infection, physical trauma, toxins, and hypoxic conditions. Furthermore, neurodegenerative diseases are prominent in the elderly population. Commonly, neural degradation is associated with a diminished neuron population or severed neuron-tissue connections. Clinical therapies for neural regeneration range from successful, PNS axonal gap connections <5.0 mm, to non-treatable, many neural degenerative diseases (Orive et al., 2009; Cunha et al., 2011). Nanomaterials are expected to revolutionize novel therapies and provide improvements to current cell-based or immunological therapies. The following sections will cover current nanomaterial compositions demonstrating CNS and PNS regeneration, and representative examples for those materials are summarized in Table 7 and some of them depicted in Figure 5.

The nervous system is vulnerable to injury, yet it is surrounded by impressive structural defenses. The skull and surrounding cerebrospinal fluid (CSF) protects the brain from trauma, and the blood–brain barrier (BBB) semi-permeable membrane guards against ROS and pathogens. The spinal vertebrates encase the vital nerves and provide structural support. The peripheral nerves lack the same protective measures, but have intrinsic regenerative capabilities (Cunha et al., 2011). Nonetheless, the CNS is at serious risk when its defenses are overwhelmed and peripheral nerve regeneration is unreliable in moderate-severe destruction. Most cell-based therapies are limited by poor cell engraftment and survival (Orive et al., 2009). Nanofiber scaffolds can establish an environment suitable for cell proliferation and survival, and promote proper neurite and axonal architecture (Ellis-Behnke et al., 2009; Orive et al., 2009). Neuroprotective drugs that are intended to minimize inflammation are ineffective via systemic injections due to the BBB and non-specific tissue distribution. The physical characteristics, primarily size and shape, of metal NPs and nano-structures confer penetrance of the BBB. Furthermore, metallic NPs are chemical stable and readily modifiable for surface functionality (Jo et al., 2015; Paviolo and Stoddart, 2015). Nanotechnology is demonstrating its potential to maximize cellular regeneration and minimize complications attributed to current methodologies (Orive et al., 2009; Cunha et al., 2011; Paviolo and Stoddart, 2015).

Peripheral nerve dysfunction is usually gradual, starting with pain sensations that progress to inconsistent coordination, which can lead to paralysis. In a study by Zhan and colleagues, a self-assembly peptide nanofiber scaffold (SAPNS) with an artery conduit sheath was implanted on the proximal and distal nerve stumps to bridge a 10 mm gap in adult rats (Zhan et al., 2013). It was found that after 16 weeks, the artificial nerve graft promoted myelination, satellite cell migration, and axonal growth over the conduit. In addition, assessment of the injured hindlimb motor function displayed significant improvement just after 6 weeks and followed throughout the 15-week period (Zhan et al., 2013). SAPNS have been of interest for axon regeneration over the last decade, initiated by Ellis-Behnke and colleagues (Ellis-Behnke et al., 2006, 2009). The self-assembly peptide hydrogels resolve the architectural issue associated with the degraded tissue environment, suitable for CNS and PNS repair. The dynamic features of self-assembling peptides have been shown to induce functional recovery in different CNS injury models (Sang et al., 2015). Modifications to SAPNS are currently being investigated to enhance their regenerative potential (Cunha et al., 2011). A nanofiber guidance channels comprised PCL/PLGA with SAPs were implanted into cysts of mice with spinal cord injury. The assessment after 6 months displayed new tissue formation, comprising nerve fibers, ECM, and a vascular network. Furthermore, the motor function had improved in the animals after the procedure. The neuro-prosthetics was positively received with and without the addition of GFs, and inflammatory response was decreased during the period (Gelain et al., 2011).

The implications of NPs and NP structures (dendrimers, liposomes) on neural regeneration are showing great promise (Provenzale and Silva, 2009; Paviolo and Stoddart, 2015; Vidal and Guzman, 2015). NPs are very flexible in design ranging from solid or hollow cores, varying shapes and sizes, and different compositions (Jo et al., 2015). It is this leniency in parameters that allows for a certain type of NP to function in a particular manner (Provenzale and Silva, 2009; Jo et al., 2015). Metallic NPs, specifically gold, have intrinsic bioactivity promoting angiogenesis and cell differentiation (Paviolo and Stoddart, 2015). Furthermore, AuNPs have bioelectric functionality providing modulation of action potentials and ion channels in nerves (Zhang et al., 2012; Paviolo and Stoddart, 2015). In a study by Das et al. (2015), a composite scaffold comprised AuNPs and silk-fibroin nanofibers (GNP-SF) was implanted into the sciatic nerve of Sprague-Dawley rats to bridge a 10 mm gap. The GNP-SF scaffolds, seeded with Schwann cells, provided significant improvements to motor function and electrical stimulation in 9- and 18-month studies. The scaffold was biocompatible and structurally stable over the study period, exemplary based on the sciatic nerve index (SNI) analysis (Das et al., 2015). Alternatively, polymeric NPs and liposomes are excellent carriers for drugs, genes, and GFs for CNS/PNS treatments (Paviolo and Stoddart, 2015; Takeda and Xu, 2015). The surface–environment interactions, modified or unmodified, with these materials are suitable for membrane penetrance, targeted tissue distribution, and biofunctional activity. Encapsulation of neuro-regenerative contents is in parallel with the material fabrication, making the procedure relatively straightforward. In addition, NPs are modifiable for in vivo monitoring, which is beneficial for assessing material regenerative potential or distribution in long-term studies.

Methods for CNS and PNS neural regeneration share a common goal, but the differences in complexity and injury severity between systems leads to divergence in applicable nanomaterials. Most PNS injury models involve precise incision and removal of segments in sciatic and peroneal nerves (Siemionow et al., 2010). Nanomaterials are designed as nerve conduits or artificial prosthetics that bridge the gap and propagate cellular proliferation, migration, and differentiation at the treated site (Siemionow et al., 2010; Cunha et al., 2011). CNS injury is far more diverse depending on the associated cause(s). For spinal cord injuries, dorsal vertebrate trauma (1–2 vertebrate at most) is common in animal models. Anatomical and functional analysis is prioritized with scaffolds employing properties that establish neo-tissue environments. Brain injury depends on the treatment, varying in degree with hypoxia-induced models or severance of specific neural circuits and cell populations (Orive et al., 2009). Primarily in brain injuries, nanotechnologies are used for sustained delivery of neurotrophic drugs or ECM-mimetic scaffolds for localized cell populations (Orive et al., 2009; Mishra et al., 2014; Jo et al., 2015). Regenerative solutions for severe spinal injury and widespread degradation of neuronal cell populations in the brain are the most challenging tasks. This movement will be facilitated in the presence of new tools and techniques that interplay with intercellular and extracellular mechanisms involved in axonal growth and extension afflicted by disease.

Treatment for structural and functional nervous tissue restoration is a massive undertaking. There is still much to learn from the biochemical, cellular, and genomic/proteomic mechanisms involving neural regeneration. This is a clear limitation in understanding nanomaterial-tissue interactions. Future studies need to elaborate on the endogenous mechanisms at play on the material interface to properly assert regenerative significance (Orive et al., 2009). Essentially, this understanding can perpetuate the novelty of nanomaterial designs to mimic these mechanisms. In addition, hybrid/composite nanomaterials can hopefully exploit bioelectric cell features and reestablish the myelin sheath. Nonetheless, nanomaterials under in vivo investigation are already complying with necessary properties for clinical translation; biocompatibility, biodegradation, low toxicity and immunogenicity, and functional surfaces/interiors are key for advancing model cases into treatment options.

The progression in nanomedicine for CNS/PNS regeneration is exciting and substantial, yet realistically the gains only permit small-scale clinical relevance. At this time, encapsulated cell-based therapies with neurotrophic factors or GFs are in clinical phase trials for CNS disorders (Orive et al., 2009). Biomaterial nerve guidance conduits for PNIs are clinically approved and in phase trials, yet most are quite short or are quickly degradable (Daly et al., 2012). The foundation for nanotechnology is being built everyday, and eventually their unique features will be fully understood and applied in next generation nervous system therapies.