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Silks are biodegradable, biocompatible, self-assemblying proteins that can also be tailored via genetic engineering to contain specific chemical features, offering utility for drug and gene delivery. Silkworm silk has been used in biomedical sutures for decades and has recently achieved Food and Drug Administration approval for expanded biomaterials device utility. With the diversity and control of size, structure and chemistry, modified or recombinant silk proteins can be designed and utilized in various biomedical application, such as for the delivery of bioactive molecules. This review focuses on the biosynthesis and applications of silk-based multi-block copolymer systems and related silk protein drug delivery systems. The utility of these systems for the delivery of small molecule drugs, proteins and genes are reviewed.
Silk proteins are produced by a variety of insects and spiders, and form fibrous materials in nature, such as spider orb webs and silkworm cocoons . The functions of silk proteins in nature range from development (cocoons), prey capture (spider webs), to safety lines (spider dragline) [2-4]. Several properties of silk-based materials, such as mechanical properties, solubility, and biodegradability, can be controlled by manipulating the secondary structure [5,6]. Silk proteins have therefore been used as medical sutures because of their mechanical properties and biocompatibility , and has also been explored as a biomaterial for cell culture and tissue engineering [2,7]. The biological properties and functions of silkworm and spider silks, which are the most studied silk proteins, are explained separately in the following sections.
Silkworm silk has been used as biomedical sutures for decades, and in textile production for clothing for centuries, because silkworms are easier to domesticate and obtain silk in comparison to spider silks. The silk fibroin from the cocoon of silkworm Bombyx mori, the most studied silkworm silk proteins, contain two major components, light (~25 kDa) and heavy chain (~325 kDa) fibroins. The core sequence in the heavy chain include alanine-glycine repeats. In silkworm cocoons, these two fibroins are encased in a sericin coat, glue-like proteins, to form the composite fibers of the cocoon. Recently, methods to extract and regenerate silk fibroin have been developed [7-13], and several silk-based biomaterials, such as silk porous scaffolds, silk films, hydrogels, and electrospun nanofibers, can be processed from silk solutions (see section 4).
The most widely studied spider silk in terms of structure and function is dragline silk from the spider Nephila clavipes [14-17]. The dragline silk is secreted as a mixture of two proteins from specialized columnar epithelial cells of the major ampullate gland of orb-weaver spinning spiders [14,18]. The molecular weights of these proteins ranges from 70 to 700 kDa depending on source. Partial cDNA clones encoding the two types of dragline silks have been isolated and analyzed from two species of orb-web weaving spiders, Araneus diadematus (ADF-3 and ADF4) and N. clavipes (MaSpI and MaSpII) [19-21]. These silk proteins are characterized as block copolymers, composed of large hydrophobic blocks with highly conserved repetitive sequences consisting of short side-chain amino acids, such as glycine and alanine, with intervening small hydrophilic blocks with more complex sequences that consist amino acids with bulkier side-chain and charged amino acids [22,23]. The hydrophobic blocks form beta-sheets, or physically cross-linked crystalline domains in silk fibers. The impressive tensile strength of silk fibers is due to the ordered hydrophobic and less ordered hydrophilic regions, in combination with chain orientation achieved during spinning [24,25].
In the last decade, remarkable progress has been made in understanding silk genetics, structures and biophysics [19,20,26]. Cloning and expression of native and synthetic silks has been achieved in a variety of host systems using synthetic oligonucleotide versions of consensus repeats or variants of these repeats garnered from sequence data from native genes [21,27,28]. Silk proteins modified by genetic engineering can also be designed to display new features alongside native properties, (Table 1) [3,29-36].
Silkworm silk from B. mori silkworm (silk-like repeats of GAGAGS) and elastin block (GVGVP) copolymers, silk-elastin-like proteins (SELP) constructed by recombinant DNA techniques, have been utilized as gene and drug delivery systems, by forming hydrogels to release adenovirus containing reporter genes [29-31,37-41]. Enhanced gene expression was reported in target cells, up to 10 fold, when compared to viral injection without the SELP, demonstrating utility for head and neck solid tumors [40,41]. Several reviews on the preparation and application of SELPs are available [30,37,38].
To increase cell-adhesive ability of silk fibroin for practical use as biomaterials, partial collagen and fibronectin sequences were inserted into silk fibroin from B. mori silkworm . The recombinant silk proteins were produced by transgenic B. mori silkworm . Films made from the recombinant silk proteins, especially the recombinant silk with [TGRGDSPAS]8, had six-fold higher activity than the original silk fibroin .
Silk fibroin from wild silkworm Anaphe has a much simpler amino acid composition, 60 mol% Ala and 30% Gly, in comparison to B. mori silkworm silk fibroin [43-46]. Anaphe silk fibroin may be a suitable candidate to design silkworm silk fibroin-mimetic recombinant proteins. Fusion proteins of silk fibroin from Anaphe and cell-binding motifs have been designed and synthesized using E. coli, to generate biomaterials with high cell adhesive ability when compared with collagen and Anaphe silk protein .
To control self-assembly of beta-sheet structures in silk, a spider silk sequence was modified to contain methionines adjacent to the polyalanine (beta sheet forming domain) sequence . Modified spider silk, which was 15mer of [SGRGGLGGQGAGAAAAAGGAGQGGYGGLGSQGT] consensus derived from the spidroin I sequence of N. clavipes (15 × 2632.23 Da), was bioengineered to include arginyl-glycyl-aspartic acid (RGD) cell-binding domains to enhance cell adhesion . Furthermore, an R5 peptide derived from the silaffin protein of the diatom Cylindrotheca fusiformis, which forms reproducible nanostructures and silica precipitation from silicic acid using species specific peptides known as silaffins, was added into the silk 15mer-RGD fusion proteins to generate nanocomposites for bone regeneration . Dentin matrix protein 1 (CDMP1) and the silk 15mer were combined via genetic engineering to exploit the self-assembly and material properties of silk proteins with controlled hydroxyapatite formation from CDMP1 . Also, hydrophilic [SQGGYGGLGSQGSGRGGLGGQT] and hydrophobic [SGAGAAAAAGGAGT] blocks (consensus sequence derived from the spidroin I of N. clavipes) were combined and cloned with different hydrophilic/hydrophobic block ratios . The structure and morphology of these amphiphilic block copolymers was determined and depended on the number of hydrophobic blocks . For new gene delivery systems, silk-based amphiphilic block copolymers with poly(l-lysine)  and RGD motifs have been developed to enhance the transfection efficiency via integrin-mediated endocytosis . These designs can be extended to further control targeting, size, stability and related needs for gene delivery. The recombinant silk-like polymers mentioned herein have demonstrated utility as advanced highly tailored or designed biomaterials with different features – from composite material systems to gene delivery.
Delivery of bioactive molecules and drugs in slow, sustained, controlled release formats is desirable for many applications. In addition, such delivery system would be advantageous if they were biodegradable, biocompatible, and mechanically durable and could be prepared and processed under ambient aqueous conditions to avoid loss of bioactivity of the drugs to be delivered. Silks can help address these needs, due to the self-assembly, mechanical toughness, processing flexibility, biodegradability and biocompatibility, therein presenting considerable utility for a number of human therapeutic interventions. Table 2 lists silk protein-based drug or gene delivery systems. Comprehensive studies, both in-vivo and in-vitro, have demonstrated that silk is biocompatible and less inflammatory than other common biodegradable polymers such as poly(lactide) and collagen [49,50]. Another important attribute of silks is their processability into different material format, such as films, hydrogels, nanofibers, nanoparticles, and three-dimensional porous scaffold [8,9,51-57]. The ability to regulate the structure and morphology of silk proteins in an all-aqueous process render this family of structural proteins important candidates for drug delivery applications. The degradation rate can be adjusted by controlling the crystalline state (beta-sheet content) during processing, to regulate the release profile of bioactive molecules.
Spider silk-based block copolymers have been designed via genetic engineering and used for the delivery of bioactive molecules, such as genes and drugs (Table 1). In particular, recombinant silk proteins containing ligand molecules, selective delivery to target cells have been generated. In the case of drug delivery for cancer treatments, silk proteins containing tumor-homing peptides can be designed for specialized delivery using nanoparticles or polyplexes targeting tumor cells (Table 3). Other target delivery systems without ligands or tumor-homing peptides for direct introduction to tumor cells via injectable hydrogels or implant materials to release drugs or genes can also be considered.
The synthesis of recombinant silk-like polymers can be broadly defined in two major steps: (1) design, construction, and cloning of the genes, and (2) expression and purification of the protein polymers (Figure 1).
Synthetic genes encoding dragline silk from N. clavipes have been successfully constructed, cloned, and expressed [22,58]. The synthesis of these recombinant genes is based on the repetitive sequences found in native dragline silk genes . The methods for construction of these repeats were previously reported, using smaller oligonucleotide repeats and subsequent multimerization . Thus, the size and sequence of the protein generated can be controlled by the primary sequence synthesized as oligonucleotides (the building blocks). The use of synthetic gene technology to control silk protein size allows for the study on relationships between sequence length and structure-function, along with the study of novel compositions . Partial cDNA sequences from N. clavipes encoding the proteins which are repetitive in nature, such as dragline protein MaSp1 sequence [GRGGLGGQGAGAAAAAGGAGQGGYGGLGSQG], have been cloned and used to construct synthetic genes . Plasmid vectors such as pPT358, pPT317 and pET30a have been used to place the synthetic genes under the control of either bacteriophage T5 or T7 promoters and also to add [His]6 at the N-terminus of the recombinant protein to simplify purification by metal affinity chromatography [37,58,59]. Based on these recombinant DNA techniques, many block copolymers containing silk-like sequences have been synthesized by [29-36,47-49]. These variants include modified spider silks bioengineered to include RGD cell-binding domains to enhance cell adhesion, inclusion of molecular triggers to control of self-assembly, chimeric silk proteins for controlled mineralization, and silk block copolymers (Table 1) [29-36,47-49].
Expression of the encoded proteins in E. coli has been successful [22,33,48,49,58]. E. coli BL21, JM109, SG13009 pREP4, and RY-3041 have been used as host systems, and yields of proteins were inversely correlated with the size of the synthetic genes. In general, expression levels obtained from synthetic silk genes are low, with yields of purified protein from 1 to 10 mg/L, representing usually less than 5% of the total protein in the cell, depending upon the size of the protein. However, the exception to these low yields appears in yeast, with 300 to 1000 mg/L in Pichia Pastoris encoding spider silks [60,61].
After protein expression, cells are harvested by centrifugation and the cell pellets are resuspended and lysed in denaturing buffer such as urea, guanidinium chloride, or guanidinium thiocyanate [5,33,48,49]. Purification of the expressed proteins has been performed by metal affinity chromatography, such as with nickel-nitrilotriacetic acid (Ni-NTA) and [His]6 systems. His-tag purification of the proteins is performed by addition of Ni-NTA agarose resin to the supernatant (batch purification) under denaturing conditions. After washing the column with denaturing buffer at pH 6.3, the proteins are eluted with denaturing buffer at pH 4.5 (without imidazole). Purified samples are extensively dialyzed against acetic buffer or NH4HCO3 solution, and then Milli-Q water .
The reconstituted dragline silk proteins from the spider Araneus diadematus have been used to prepare microcapsules for drug delivery using self-assembly of the proteins at an emulsion interface . These microcapsules were suggested to be useful to encapsulate small active ingredients, provided that the active ingredient does not impede the adsorption of the silk and/or that the encapsulation process does not alter the ingredient . Microspheres of bioengineered spider silks, which were derived from ADF4 from A. diadematus, were formed by several methods such as dialysis and micromixing . As a result of their material strength, biocompatibility, and the possibility of functionalization via recombinant protein techniques, spider silk microspheres may offer potential for the development of targeted drug delivery systems.
In previous studies, a silk-based block copolymer was generated by combining spider silk consensus repeats with poly(l-lysine) for gene delivery . Poly(l-lysine) is a cationic polymer that interacts with DNA through electrostatic interactions to assemble into polyelectrolyte complexes, is degraded in cells and has been used as an alternative to recombinant viruses for the delivery of pDNA into cells [64-66]. The silk-based block copolymers formed ion complexes with pDNA (Figure 2), and the sizes were controllable based on the polymer/DNA ratio or molecular weight of poly(l-lysine) bioengineered into the designs . The sizes of pDNA complexes prepared at copolymer/pDNA ratio of 10 ranged from 310 to 590 nm. Also, the pDNA complexes of silk-based block copolymers with less than 30 lysines showed no cytotoxicity toward human embryonic kidney (HEK) cells. This study demonstrated the feasibility of bioengineering highly designed silk-based pDNA complexes for gene delivery systems; however, the transfection efficiency was too low to be useful for gene vectors.
Silk-based block copolymers are potentially useful candidates for nonviral gene vector, because various functional peptides such as cell binding motifs (RGD), cell penetrating peptides [67-69], signal peptides of virus , and/or tumor-homing peptides [71-75] can be added as ligands through recombinant DNA techniques, an important advantage of recombinant silk proteins over liposomes and synthetic polymers as gene delivery systems as shown in Figure 3. Silk-based block copolymers can contain several modules based on the molecular design for specific target delivery, and also regulate sizes, drug release rates, and zeta potentials of complexes of the copolymer and bioactive molecules. Several functional peptides are briefly reviewed, since they may be potentially useful for target gene/drug delivery systems (Table 4).
In the case of gene delivery, transfection of silk-based polymers that contain ligand molecules is expected via receptor-mediated endocytosis (Figure 4). The RGD sequence, arginyl-glycyl-aspartic acid, is known to selectively recognize and bind αvβ3 and αvβ5 integrins that are expressed on cell surfaces of certain cell types such as endothelial cells, osteoclasts, macrophages, and platelets [76-79]. The integrins are considered to be a class of transmembrane glycoproteins that interact with the extracellular matrix, and are exploited for cell-binding and entry by receptor-mediated endocytosis, a representative pathway for gene delivery . RGD sequences are therefore a useful candidate as a ligand for gene vectors. Based on the properties of RGD, the biocompatible, biodegradable, and non-toxic cationic polymers with the addition of RGD were exploited to enhance transfection efficiency of silk-based gene vectors via the integrin-mediated endocytosis . Globular complexes of these recombinant silks modified to contain RGD cell-binding motifs with pDNA were prepared for in-vitro gene delivery to HeLa and HEK cells. The pDNA complexes of recombinant silk protein with 30-lysine residues and 11 RGD sequences prepared at the ratio of number of amines/phosphates from pDNA (N/P) of 2, which were positively charged particles of approximately 186 nm in diameter, showed the highest efficiency to HeLa cells of the recombinant silks examined because of integrin-mediated transfection with 11 RGD sequences. However, recombinant silk proteins with few RGD sequences showed low transfection, suggesting that a few RGDs are not enough to be recognized by integrin receptors at the cell surface membrane. The position of RGD motif, at the N- or C-terminus of the recombinant silks, did not influence the transfection efficiency of the pDNA complexes.
Tumor vasculature, which is important in cardiovascular diseases and cancer, is a target for anticancer therapy, however, most carriers for gene or drugs are relatively poor at specific delivery to specific cells. Selective targeting to tumor cells has been reported using several tumor-homing peptides (Table 4). Peptides include antibodies that recognize tumor-specific vascular signatures, identified by in-vivo screening of phage libraries, revealed extensive heterogeneity in tumor blood vessels and lymphatics [80-82]. The functions of tumor-homing peptides are summarized in other reviews .
Cell-penetrating peptides (CPPs) can be defined as short peptides that are able to efficiently penetrate cellular lipid bilayers or destabilize cellular membrane. Therefore, CPPs are useful candidates for new nonviral vectors of oligonucleotides, shRNA, double strand and plasmid DNA. Recent data of the CPP internalization mechanisms suggest that endocytosis contributes to the uptake, clathrin-dependent endocytosis and macropinocytosis have been suggested to mediate CPP translation [69,84-87]. There are also reports claiming that cellular uptake is independent of endocytotic pathways and occurs through transient pore formation [88-91]. Additionally, it has been suggested that CPPs simultaneously utilize different mechanisms of endocytosis and uptake occurs by an additional rapid translocation process . Various CPPs have been reported, and some of them are listed in Table 4. One of the highest transfection efficiencies of pDNA complexes with cell-penetrating peptides was reported to be approximately 45-fold higher in comparison to the pDNA complex of polyethyleneimine at low DNA concentration (125 ng/mL) . CPPs have been previously reviewed [83,93-95]. Recombinant silk proteins containing CPP (ppTG1) and their pDNA complexes were prepared for in-vitro gene transfection to HEK cells . The recombinant silk protein containing a dimer of ppTG1 showed higher transfection efficiency, almost identical to lipofectamine 2000, in comparison with the other silk-based gene vectors . Thus, significant improvements are anticipated upon addition of such peptides as an approach to enhance transfection efficiency.
Several virus-derived peptides, such as signal peptides and capsid proteins, have been studied for gene delivery [70,97,98]. Adenovirus infection is mediated predominantly by the penton and fiber capsid proteins. These proteins interact with cellular factors to coordinate key events that permit the passage of viral particles into the cell and subsequently to the nuclear periphery for gene transfer (Figure 4). Key to infection efficiency is the outer protein coat or capsid . One of the earliest targeted systems, which utilized polylysine for DNA transport, produced high levels of receptor binding and internalization but relatively low transgene expression . It was also suggested that the viral capsid itself promotes cytosolic entry in the absence of viral gene expression [101-103]. These functions of signal peptides and capsid proteins can be taken into consideration in the development of gene and drug transport systems with silks for improved delivery.
Silkworm silk has been used as biomedical sutures because of its biocompatibility and mechanical strength. However, virgin silk with the associated contaminant sericin proteins is a potential allergen causing a Type I allergic, due to upregulated IgEs in response to the sericins [104-109]. Once the sericins are properly removed, there is minimal response from the core fibroin structural proteins, as described earlier. The degradation product of silk fibroin proteins with beta-sheet structures from the action of proteases, such as alpha-chymotrypsin, has recently been reported, and no cytotoxicity was observed to neuron cells in-vitro . Removal of sericin from virgin silkworm silk is therefore necessary to prepare non-allergic response and non-cytotoxic silk-based materials. Methods to extract and regenerate silk fibroin have been developed [7-13]: cocoons of B. mori silkworm silk are boiled for 30-60 min in an aqueous solution of 0.02 M Na2CO3 and then rinsed with MilliQ water to extract the sericin proteins. The extracted silk is then dissolved into 9.3M LiBr solution at 60°C, yielding a 20 wt% silk solution. The silk solution is dialyzed in MilliQ water using dialysis membrane with MWCO of less than 3,500 for more than 48 h. According to this basic method, approximately 7-8 wt% silk solutions are obtained. Also, silk sponges, which are obtained from silk solution after lyophilization, can be dissolved in hexafluoro-2-propanol (HFIP). Several silk-based biomaterials can be processed from silk solutions (Figure 5). For instance, aqueous-derived and HFIP-derived silk porous scaffolds have been prepared using salt leaching, gas forming, or freeze drying method [10-13]. Silk films are prepared by cast or layer-by-layer deposition of silk aqueous or HFIP solution with various concentrations [51,111,112]. Hydrogels of silk fibroin are formed via sol-gel transitions by sonication, vortexing, or the presence of acid and/or ions [53,54,113]. Nanofibers of silk fibroin can be prepared by electrospinning . For silk-based materials, methanol can be used to induce beta-sheet structure in the materials, which makes them water-insoluble and slower-biodegradable . Alternatively, water annealing has also been developed for such transitions, avoiding the use of any organic solvents .
Silk-based 3D scaffolds are attractive biomaterials for bone tissue regeneration because of their biocompatibility and mechanical properties [2,114]. The 3D silk fibroin scaffolds loaded with bone morphogenetic protein-2 (BMP-2) were successfully developed for sustained release of BMP-2 in order to induce human bone marrow stromal cells to undergo osteogenic differentiation when the seeded scaffolds were cultured in-vitro and in-vivo with osteogenic stimulants for 4 weeks . Horseradish peroxidase (HRP) enzyme gradients were also immobilized on silk 3D scaffolds to prepare new functional scaffolds including regional patterning of the gradients to control cell and tissue outcomes . Recently, adenosine release via silk-based implants to the brain has been studied for refractory epilepsy treatments [116,117]. Silk-based implants to release adenosine demonstrated therapeutic ability, including the sustained release of adenosine over a period of two weeks via slow degradation of silk, biocompatibility, and the delivery of predetermined dose of adenosine . Nerve growth factor (NGF)-loaded silk fibroin nerve conduits have been studied to guide the sprouting of axons and to physically protect the axonal cone for peripheral nerve repair . NGF release from the differently prepared silk fibroin-nerve conduits was prolonged over 3 weeks, while the total amount of NGF released depended on the drying procedures used in the preparation of the nerve conduits, such as air drying or freeze drying . Silk fibroin scaffolds containing insulin-like growth factor I (IGF-I) were prepared for controlled IGF-I release in the context of cartilage repair . Chondrogenic differentiation of human bone marrow-derived mesenchymal stem cells (hMSCs) was observed, starting after 2 weeks and more strongly after 3 weeks . Tropical tasar silkworm Antheraea mylitta silk-based 3D matrices were also evaluated for in-vitro drug release and for the study of cell-surface interactions [120,121]. The silk-based matrices contained two different model compounds, bovine serum albumin (66 kDa) and FITC-inulin (3.9 kDa), to characterize release profiles . Silk fibroin protein blended calcium alginate beads resulted in prolonged drug release without initial burst for 35 days as compared to calcium alginate beads without silk fibroin . Additionally, silk-based micromolded matrices supported a significant enhancement in cell attachment, spreading, mitochondrial activity, and proliferation with feline fibroblasts in comparison to polystyrene plates as controls . These studies indicate the potential use of slow degrading silk fibroin 3D scaffolds and tubes loaded with bioactive molecules such as BMP, HRP, and adenosine for drug-releasing biomaterials.
Silk films have been used with covalent decoration of functional peptides as implants for bone formation and drug delivery. For bone regeneration, BMP-2, RGD, and parathyroid hormone (PTH) can be directly immobilized on silk films using carbodiimide chemistry [8,10]. Differentiation of human bone marrow-derived stem cells cultured with the decorated silk films was induced by immobilized BMP-2. Also, the utility of silk films to promote long-term adenosine release from adenosine kinase deficient embryonic stem cells has been investigated [122,123]. These studies demonstrated that silk fibroin constitutes a suitable material for the directed differentiation of embryonic stem cells and for cell-mediated therapeutic release of adenosine. Silk films decorated with bioactive molecules could therefore be used for local drug delivery via direct implantation.
Silk films have also been used to promote stabilization of entrained molecules such as enzymes or therapeutic proteins . Glucose oxidase, lipase, and HRP were entrapped in silk films over 10 months and significant activity if the enzymes were retained, even when stored at 37°C. Silk films result in stabilization of enzymes without the need for cryoprotectants, emulsifiers, covalent immobilization or other techniques. Further, the stabilization of enzymes in silk films is amenable to environmental distribution without refrigeration, and offers potential use in-vivo such as the delivery of bioactive molecules.
Scaffolds for tissue engineering may mimic the structure and biological function of the extracellular matrix. The natural extracellular matrix is a composite material with fibrous collagens embedded in proteoglycans. The collagen fibers are organized in a 3D porous network that form hierarchical structures from nanometer length scale multi-fibrils to macroscopic tissue architectures [125,126]. The structures generated by electrospinning contain nanoscale fibers with microscale interconnected pores, resembling the topographic features of the extracellular matrix. Therefore, silk fibroin fiber scaffolds formed by electrospinning have potential as scaffolds. Silk fibroin fiber scaffolds containing BMP-2 and/or nanoparticles of hydroxyapatite (HAP) prepared via electrospinning have been studied for in-vitro bone formation from hMSCs . The bioactivity of BMP-2 was retained after the aqueous-based electrospinning process, and the nanofibrous electrospun scaffolds with co-processed BMP-2 supported high calcium deposition and enhanced transcript levels of bone-specific markers, indicating that the electrospun scaffolds were an efficient delivery system for HAP nanoparticles and BMP-2.
Drug delivery systems via silkworm silk-based nanoparticles have been investigated [128-130]. Biologically derived silk fibroin-based nanoparticles (<100 nm) for local and sustained therapeutic curcumin delivery to cancer cells were fabricated by blending with noncovalent interactions to encapsulate curcumin in various proportions with pure silk fibroin or silk fibroin with chitosan . Silk nanoparticles from silk fibroin solutions of domesticated B. mori and tropical tasar silkworm A. mylitta were stable, spherical, negatively charged, 150-170 nm in average diameter and showed no toxicity . The silk nanoparticles were observed in the cytosol of murine squamous cell carcinoma cells, and the growth factor release from the nanoparticles showed significantly sustained release over 3 weeks, implying potential application as a growth factor delivery system . The silk-based nanoparticles containing curcumin showed a higher efficiency against breast cancer cells and have potential to treat in-vivo breast tumors by local, sustained, and long-term therapeutic delivery. Silk sericin-poloxamer nanoparticles loaded with both hydrophilic and hydrophobic drugs were reported to be stable in aqueous solution, small size (100-110 nm) and rapidly taken up by cells .
Silk fibroin microspheres were processed using spray-drying, however, the sizes of the microspheres were above 100 μm, which is suboptimal for drug delivery . Other methods to prepare silk microspheres include lipid vesicles as templates to efficiently load bioactive molecules for local controlled releases was reported recently . The lipid is subsequently removed by methanol or NaCl, resulting in silk microspheres consisting beta-sheet structure and approximately 2 μm in diameter . The silk microspheres loaded with HRP, used as a model drug, demonstrated controlled and sustained release of active enzyme over 10-15 days. Growth factor delivery via the silk microspheres in alginate gels was also reported to be more efficient in delivering BMP-2 than insulin-like growth factors, probably due to the sustained release of the growth factor . Additionally, growth factors successfully formed linear concentration gradients in scaffolds to control osteogenic and chondrogenic differentiation of hMSCs during culture. This silk microsphere/polymeric scaffold system is an option for the delivery of multiple growth factors with spatial control for in-vitro and in-vivo 3D cultures. In more recent studies, a new mode to generate micro- and nanoparticles from silk, based on blending with polyvinyl alcohol was reported . This method simplifies the overall process compared with lipid templating and provides high yield and good control over the feature sizes, from 300 nm to 20 μm, depending on the ratio of polyvinyl alcohol/silk used . Silk fibroin microparticles containing BMP-2, BMP-9, and BMP-14 were prepared by dropwise addition of ethanol, and exhibited mean diameters of 2.7 ± 0.3 μm, encapsulation efficiencies of 67.9-97.7% depending on the type and amount of BMP loaded, and slow release of BMPs for 14 days .
There is a critical need in medicine to develop simple and versatile methods to assemble robust, biocompatible, and functional biomaterial coatings that direct cell outcomes. Coatings of silk fibroin have been studied to provide interfaces for biomaterials [111,112,136,137]. The driving force of self-assembly to form coatings is hydrophobic and some electrostatic interactions. The flexibility of silk-based coatings has been investigated using an aqueous stepwise deposition process with B. mori silk solution, which can control the structure and stability of the silk fibroin in layer-by-layer films . The thickness of one layer was reported to be around 10 nm when deposited from a 1 mg/mL silk aqueous solution. The secondary structure of silk fibroin in the coatings was regulated to control the biodegradation rate, which indicates that release of drugs from these coatings can be controlled via layer thickness, numbers of layers and secondary structure of the layers. The silk coatings have also been formed on poly(lactide-co-glycolic acid) (PLGA) and alginate microspheres for protein delivery . The silk coatings on PLGA microspheres was reported to be ~1 μm and discontinuous, while those on alginate microspheres was ~10 μm thick and continuous. These coatings provide mechanically stable shells as well as a diffusion barrier to the encapsulated protein drugs . Nanolayer coatings of silk fibroin to contain model compounds of small molecule drugs and therapeutically relevant proteins, such as rhodamine B and azoalbumin, have been prepared using the stepwise deposition method . Multilayered silk-based coatings have been developed and used as drug carriers and delivery systems to evaluate vascular cell responses to heparin, paclitaxel, and clopidogrel . Cell attachment and viability with human aortic endothelial cells and human coronary artery smooth muscle cells on the drug-incorporated silk coatings demonstrated that paclitaxel and clopidogrel inhibited smooth muscle cell proliferation and retarded endothelial cell proliferation . The silk multilayers with heparin promoted human aortic endothelial cell proliferation while inhibiting human coronary artery smooth muscle cell proliferation, which was a desired outcome for the prevention of restenosis . Solid adenosine powder coated with silk fibroin were investigated for local and sustained delivery of the anticonvulsant adenosine from encapsulated reservoirs . Reservoir coating thickness was varied through manipulation of the silk coating solution concentration and the number of coatings applied. An increase in either coating thickness or crystallinity delayed adenosine burst, decreased average daily release rate, and increased the duration of release . These reports demonstrate that the silk coating is an effective system for drug-eluting coatings, such as for stem applications, based on its useful micromechanical properties and biological outcomes.
Silk-based biomaterials to deliver bioactive molecules, such as small drugs, proteins, and genes, are described in this review. The remarkable mechanical properties, versatile processing in an aqueous environment, biocompatibility, and controlled degradation suggest silks (both native as well as recombinant) are attractive biomaterials for controlled and sustained release, stabilization and delivery of bioactive molecules. Silk solutions can be morphed into a variety of biomaterial formats, including films, 3D porous scaffolds, hydrogels, micro- and nano-spheres, nanofibers, and coatings. The degradation rate of these biomaterials can be also controlled during processing, by the secondary structures. In addition to these useful properties, silk proteins derived from recombinant DNA technology can be bioengineered for highly tailored chemistries, greatly expanding the suite of options for targeted delivery. Targeted-delivery function is a significant factors in drug delivery, hence, these silk proteins can be prepared with functional sequences to hone to specific cells, tissues or organs, as a useful strategy for silk-based delivery systems with bioactive molecules. When combined with the novel features of the silk proteins themselves, including self-assembly, robust mechanical properties, water-based processing, controlled biodegradation and biocompatibility, silks offer a unique and versatile delivery platform for small molecules, large proteins, DNA and RNA. Hybrid or composite silk-based materials containing other biopolymers, have not been extensively studied, yet should provide applicable mechanical, thermal, and biological properties for not only drug/gene delivery but also for tissue engineering, medical imaging, and regenerative medicine.
The authors thank Carmen Preda (M.Sc.), Dean L. Glettig, Dr. Michael Lovett, Eleanor Pritchard, and Dr. Aneta J. Mieszawska for providing the images in Figure 5. This work has been supported by grants from the NIH (Tissue Engineering Resource Center), the NSF and the AFOSR (D.K.). K.N. was supported by a Japan Society for the Promotion of Science Postdoctoral Fellowship for Research Abroad.
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