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To evaluate the toxicity and cellular uptake of both undifferentiated and differentiated human adipose-derived stem cells (hASCs) exposed to silver nanoparticles (Ag-NPs), and to assess their effect on hASC differentiation.
hASC were exposed to 10- or 20-nm Ag-NPs at concentrations of 0.1, 1.0, 10.0, 50.0 and 100.0 μg/ml either before or after differentiation down the adipogenic or osteogenic pathways.
Exposure of hASC to either 10- or 20-nm Ag-NPs resulted in no significant cytotoxicity to hASC, and minimal dose-dependent toxicity to adipogenic and osteogenic cells at 10 μg/ml. Each of the hASC, adipogenic and osteogenic cells showed cellular uptake of both 10- and 20-nm Ag-NPs, without causing significant ultrastructural alterations. Exposure to 10- or 20-nm Ag-NPs did not influence the differentiation of the cells, and at antimicrobial concentrations of Ag-NPs resulted in a minimal decrease in viability.
The biocompatibility of Ag-NPs with both undifferentiated and differentiated hASC establishes their suitability for incorporation into tissue-engineered graft scaffolds, for the prevention of bacterial contamination upon implantation.
Over 300,000 incidences of surgical-site infection occur annually in the USA, arising in approximately 2–3% of patients who have undergone surgery. Although rates vary widely according to the type of surgery, 33% of infections occur from orthopedic surgeries resulting in increased treatment intensity, prolonged length of stay, higher costs and greater risk for readmission or death . The most common bacterial strain responsible for surgical infection is Staphylococcus aureus, and the only method employed currently to avoid infection is through strict adherence to sterile surgical conditions and through the administration of prophylactic antibiotics . However, drug-resistant organisms such as methicillin-resistant S. aureus and vancomycin-resistant enterococci are still problematic .
Due to the enhanced antibacterial activity of silver (Ag) at the nanoscale level, Ag-nanoparticles (NPs) are the most used nanomaterial and the most valuable in the medical and personal hygiene fields through their incorporation into hundreds of consumer products . Previous studies have demonstrated that Ag-NPs exert antimicrobial effects on a wide spectrum of bacteria such as Escherichia coli, Enterococcus faecium, Vibrio cholera, S. aureus and even methicillin-resistant S. aureus [2–4]. Since Ag compounds have been used for centuries with a lack of toxicity or carcinogenicity to the immune, cardiovascular, nervous or reproductive systems, the use of Ag-NPs in products has largely been unregulated . Presently, there is no consensus on the cytotoxicity of Ag-NPs; however, the majority of publications do show reduced cell viability and increased reactive oxygen species generation following Ag-NP exposure .
An application for Ag-NPs is their incorporation into implantable materials such as prostheses and skin or bone grafts. In recent years, tissue engineering of patient-specific bone grafts has been used to replace damaged or defective tissues, and has become a viable alternative to autografts and allografts . Advances in human stem cell research demonstrate that these cells have unique properties that are important for the development of engineered tissue constructs, including high proliferation rates and self-renewal capacity, maintenance of the unspecialized state, and specialized differentiation under given conditions. Human mesenchymal stem cells (hMSCs) isolated from either adult bone marrow or adipose tissue possess a high capacity for self-replication and have the potential to differentiate into osteogenic, chondrogenic, adipogenic and tenogenic lineages when placed in an appropriate environment [7,8].
The interaction and metabolism of Ag-NPs with cultured osteoblasts grown from hMSC should be minimal for their incorporation into a scaffold to be successful. A number of studies have shown that various mesoporous silica and magnetic NPs used for cell tracking have no apparent deleterious effects on the morphology, cell proliferation, cell viability and differentiation efficiency of stem cells [9–11]. However, Ag-NPs and Ag ions have been reported to attach to cell membranes, and interact with cellular molecules such as DNA, bacterial cell wall components or sulfhydryl groups of metabolic enzymes [2–4]. Therefore, bacterial replication, membrane permeability, and different metabolic pathways may be interrupted. The objective of this study was to evaluate the toxicity and cellular uptake of both undifferentiated and differentiated human adipose-derived stem cells (hASCs) exposed to Ag-NPs, and to assess their potential effect on hASC differentiation. Understanding the interactions between Ag-NPs and undifferentiated hASC is important to determine whether the antimicrobial activity of Ag-NPs is detrimental to the differentiation of hASC down the adipogenic or osteogenic pathways for tissue engineering scaffold systems.
Two solutions of spherical Ag-NPs were obtained from NanoComposix (CA, USA), each at Ag-NP concentration of 1.00 mg/ml with diameters of 10 and 20 nm. Ag-NPs were synthesized by ammonium hydroxide-catalyzed growth of Ag onto 5-nm gold-seed particles. Concentration of the particles was achieved via tangential flow filtration. The Ag-NPs were then serially washed with 20 volume equivalents of phosphate buffer (PB), resuspended in stabilizing citrate buffered deionized (DI) water and stored at 4°C in the dark.
Particle size was determined by dynamic light scattering (DLS) and transmission electron microscopy (TEM) to confirm the manufacturer-identified diameters. To measure the hydrodynamic diameters and the ζ-potential, samples of Ag-NPs were suspended at the highest dosing concentration in DI water, immediately placed in a disposable cuvette and analyzed using a Zetasizer Nano-ZS (Malvern Instruments, Inc., Worcestershire, UK). The DLS readings were performed at the standard characterization temperature of 25°C. Each measurement was repeated five-times, with ten to 20 runs as optimized by the instrument. Data was culled based on the correlogram, size quality report and expert advice rendered by the Dispersion Technology Software (5.03) (Malvern Instruments Inc.). In addition, TEM was utilized to characterize Ag-NP structure, shape and size uniformity. Samples were prepared by placing a drop of homogeneous suspension of each Ag-NP solution at the highest dosing concentration in DI water onto a formvar-coated copper grid and air dried. Samples were examined on an FEI™/Philips EM 208S (FEI, OR, USA) TEM operating at an accelerating voltage of 80 kV.
All protocols involving human tissue were approved by the Institutional Review Boards of the University of North Carolina at Chapel Hill (NC, USA) and North Carolina State University (NC, USA). Excess adipose tissue from elective plastic surgery procedures was obtained with donor consent from five premenopausal female donors of Caucasian, Native American or other ethnicities who ranged from 24 to 37 years of age. The hASC were isolated from the adipose tissue by enzymatic digestion using 0.075% collagenase type I, and characterized as described in [12,13]. Cells were seeded into T-75 flasks, and grown to approximately 70–80% confluency in a 5% CO2 incubator at 37°C for expansion and culture. Cells were harvested using trypsin which increased their passage number incrementally (e.g., passage-0, passage-1 and so on). At passage-1, hASC from each of the five donors were pooled into a T-75 flask (20,000 cells/donor; 100,000 cells total), expanded and frozen in liquid nitrogen until needed.
Pooled passage-3 cells were seeded into T-75 cell culture flasks at 100,000 cells/flask, cultured in complete growth medium (minimum essential medium eagle, alpha-modified supplemented with 10% fetal bovine serum, 2 mM L-glutamine, 100 units/ml penicillin and 100 μg/ml streptomycin), and maintained at 37°C in a humidified atmosphere of 5% CO2. Once hASC reached 80% confluency, after 6 days, cultures were washed twice with phosphate buffered saline and cells were retrieved using trypsin. At this point, hASC were plated into 12-well plates (5000 cells/well) to assess viability, into T-25 flasks (50,000 cell/flask) to assess cellular uptake, and into six-well plates (50,000 cells/well) to assess any Ag-NP effects on differentiation. Differentiation of cells was achieved via hASC culture in osteogenic medium (complete growth medium supplemented with 50 μM ascorbic acid, 0.1 μM dexamethasone and 10 mM β-glycerophosphate), or in adipogenic medium (complete growth medium supplemented with 1 μM dexamethasone, 5 μg/ml insulin, 100 μM indomethacin and 500 μM isobutylmethylxanthine), or in complete growth medium to maintain the cells in their progenitor cell state.
To determine the effect of Ag-NPs on both undifferentiated and differentiated hASC viability, undifferentiated hASC were grown to 100% confluency in complete growth medium for 4 days. To determine the baseline viability, hASC were first differentiated down the osteogenic and adipogenic pathways or maintained in their proliferative state for 14 days and then exposed for 24 h to concentrations of 0, 0.1, 1.0, 10.0, 50.0 and 100.0 μg/ml of either 10- or 20-nm Ag-NPs. As a comparison to examine any effect internalized Ag-NPs have on hASC, cells were first exposed for 24 h to Ag-NPs and then differentiated down the osteogenic or adipogenic pathways (or maintained in their proliferative state) for 14 days. At the conclusion of each of these alternatives, the viability of the hASC was assessed with alamarBlue® (Molecular Probes, Invitrogen, OR, USA) viability assay; this assay was chosen based upon its dye having minimal interactions with Ag-NPs . Briefly, a 10% alamarBlue solution was added to each well, incubated for 3 h and fluorescence quantitated on a Spectra Max® Gemini™ (Molecular Devices, CA, USA) EM spectro photometer at an excitation wavelength of 545 nm and an emission wavelength of 590 nm. The fluorescence values were normalized to controls and expressed as percent viability.
To view potential cellular uptake of Ag-NPs into hASC, undifferentiated hASC were grown to 100% confluency in complete growth medium for 5 days. To determine baseline uptake data, hASC were first differentiated down the osteogenic or adipogenic pathways or maintained in their proliferative state for 14 days and then exposed for 24 h to concentrations of 0, 0.1, 1.0, 10.0, 50.0 and 100.0 μg/ml of either 10- or 20-nm Ag-NPs. As a comparison to examine any morphological and ultrastructural effect internalized Ag-NPs have on hASC, cells were first exposed for 24 h to Ag-NPs and then differentiated down the osteogenic or adipogenic pathways (or maintained in their proliferative state) for 14 days. At the conclusion of each of these alternatives, cells were harvested with trypsin, rinsed in Hank’s balanced salt solution and fixed for 24 h in Trump’s fixative at 4°C. Cells were rinsed in 0.1 M PB (pH 7.2), pelleted in a microfuge tube, resuspended and quickly pelleted in 3% molten agar. Samples were postfixed in 1% osmium tetroxide in 0.1 M PB for 1 h at 4°C, washed with DI water, dehydrated through an ascending ethanol concentration, cleared in acetone, infiltrated and embedded with Spurr’s resin, and polymerized at 70°C overnight. Cells were not stained to allow for better visualization of the Ag-NPs and to ensure the absence of stain precipitate artifacts. TEM analysis was performed to determine if any morphological or ultrastructural changes occurred between untreated cells and cells exposed to Ag-NPs either prior to or following differentiation, as well as any abnormalities in intracellular lipid accumulation within adipogenic cells or extracellular calcium accretion by osteogenic cells.
To assess any effects of Ag-NPs on hASC differentiation, undifferentiated hASC were grown to 100% confluency in complete growth medium for 5 days. Then, hASC were exposed for 24 h to either 10- or 20-nm Ag-NPs at concentrations of 0, 0.1, 1.0, 10.0, 50.0 and 100.0 μg/ml, made fresh in complete growth medium. After 24 h the medium was removed, and cells were differentiated down the osteogenic or adipogenic pathways or maintained in their proliferative state for 14 days. Osteogenic differentiation was determined with Alizarin Red S staining for extracellular calcium accretion, and adipogenic differentiation was determined with Oil Red O staining for intercellular lipid accumulation. To assess differences in staining between control and treatment wells, digital light microscopy images were obtained from each well (n = 6 wells per treatment), and the pixel area per image (three images per well) covered by the stained calcium or lipid was determined by color-based image analysis using Adobe® Photoshop®.
The mean values for hASC percent viability (normalized to control) and pixel area per image for each treatment were calculated, and the significant differences (p < 0.05) determined by the PROC GLM Procedure (SAS 9.1 for Windows; SAS Institute, NC, USA). When significant differences were found, multiple comparisons were performed with the Tukey’s Studentized Range HSD test at p < 0.05 level of significance. The Dunnett’s t-test was performed to determine the significance at p < 0.05 of differences between control and treatment groups. Data were expressed as the mean ± standard error of the mean of two plates (n = 6 wells per treatment) and three images per treatment.
The physicochemical properties of the Ag-NPs can be found in Table 1, which lists the physical and hydrodynamic diameters of the Ag-NPs according to TEM and DLS, respectively, as well as the supplied Ag-NP solution concentration, particle concentration and ζ-potential. As is typical for nanomaterials, the hydrodynamic diameter of the 10- and 20-nm Ag-NPs measured by DLS was found to be slightly larger (21.7 and 27.4 nm, respectively) than the physical diameter measured by TEM (7.2 and 19.2 nm, respectively). The significantly larger hydrodynamic diameter of the 10-nm Ag-NPs is most likely attributable to the formation of small, loosely bound Ag-NP dimers. The ζ-potential of a colloid characterizes its stability and ability to resist aggregation, with greater ζ-potentials having greater stability. Both the 10- and 20-nm Ag-NPs had ζ-potentials between −40 and −50 eV, which indicated good stability. The stability and lack of aggregated clusters is largely due to the addition of stabilizing citrate buffer. According to TEM, both 10- and 20-nm Ag-NPs were found to be spherical in shape and highly uniform in size (Figure 1).
When undifferentiated hASC were exposed to 10- and 20-nm Ag-NPs for 24 h, and then differentiated for 14 days, no significant decrease in viability was observed for the undifferentiated hASC. A concentration-dependent toxicity was observed for both osteogenic and adipogenic cells starting at an Ag-NP concentration of 10 μg/ml (Figure 2A & B). Similarly, the addition of either 10- or 20-nm Ag-NPs following hASC differentiation resulted in no significant decrease in viability of undifferentiated hASC at any concentration, while concentration-dependent toxicity was observed for 10-nm Ag-NPs at 100 μg/ml for osteogenic cells and at 10 μg/ml for adipogenic cells (Figure 2C), and for 20-nm Ag-NPs at 50 μg/ml for osteogenic cells and at 100 μg/ml for adipogenic cells (Figure 2D). It should be noted that although significant decreases in viability were observed, the maximal loss of viability was only 30%.
Exposure of 10- and 20-nm Ag-NPs to differentiated hASC served as the control for the evaluation of 10- and 20-nm Ag-NP exposure to undifferentiated hASC. Any morphological and ultrastructural changes in cells, as well as changes in intracellular lipid accumulation in adipogenic cells and extracellular calcium accretion in osteogenic cells, were compared with untreated cells. It was observed that for each treatment group, approximately 50% of all cells contained Ag-NPs within their cytoplasmic vacuoles, and an increase in treatment concentration resulted in an increase in Ag-NP agglomerates within the vacuoles. Transmission electron micrographs of cells exposed to 10 μg/ml are shown as a representative sample (Figures 3–5).
Neither 10- nor 20-nm Ag-NP exposure to either undifferentiated or differentiated hASC resulted in any morphological abnormalities to cells compared with controls. Control hASC were slightly elongated and displayed indented nuclei, a prominent nucleolus and small intra-cytoplasmic vacuoles along the periphery of the nucleus (Figure 3A). Small agglomerates of 10-nm Ag-NPs were observed at low magnification within cytoplasmic vacuoles of hASC (Figure 3B), and high magnification of these vacuoles confirmed the presence of Ag-NPs through the highly uniform shape and size of the Ag-NPs (Figure 3C). Similarly, 20-nm Ag-NPs were seen in small agglomerates within vacuoles along the periphery of the nucleus (Figure 3D). High magnification confirmed numerous Ag-NPs within these vacuoles (Figure 3E).
Both 10- and 20-nm Ag-NP exposure to hASC prior to, or following, adipogenic differentiation did not result in any morphological or ultrastructural changes to cells compared with controls. Control adipogenic cells exhibited a more globular morphology with extensive lipid droplet accumulation within the cell (Figure 4A). Small agglomerates of 10-nm Ag-NPs were observed at low magnification within cytoplasmic vacuoles of unstained adipogenic cells, and Ag-NPs were not observed within the lipid droplets (Figure 4B). High magnification of these vacuoles confirmed the presence of Ag-NPs through the highly uniform shape and size of the Ag-NPs (Figure 4C). Similarly, 20-nm Ag-NPs were seen in small agglomerates within cytoplasmic vacuoles (Figure 4D), and high magnification again confirmed Ag-NPs within these vacuoles (Figure 4E).
Both 10- and 20-nm Ag-NP exposure to hASC prior to, or following, osteogenic differentiation did not result in any morphological changes to the cells compared with controls. Control osteogenic cells were more fusiform (Figure 5A), with extensive extracellular calcium accretion (Figure 5B). Numerous small agglomerates of 10-nm Ag-NPs were observed at low magnification within cytoplasmic vacuoles of the osteogenic cells (Figure 5C), and high magnification of these vacuoles confirmed the presence of Ag-NPs through the highly uniform shape and size of the Ag-NPs (Figure 5D). Similarly, 20-nm Ag-NPs were seen in small agglomerates within vacuoles (Figure 5E), and high magnification confirmed Ag-NPs within these vacuoles (Figure 5F).
Exposure of undifferentiated hASC to either 10 or 20-nm Ag-NPs for 24 h at any concentration did not influence hASC differentiation. Light micrographs of cells exposed to 10 μg/ml are shown as a representative sample (Figures 6–8).
Undifferentiated hASC were stained for calcium accretion with Alizarin Red S (Figure 6A–C), and lipid accumulation with Oil Red O (Figure 6D–F). Since the hASC were maintained in complete growth medium, control cells stained for neither calcium (Figure 6A) nor lipid (Figure 6D). There was no significant occurrence of either lipid or calcium following exposure to 10-nm Ag-NPs at any of the concentrations as evidenced by a lack of calcium and lipid staining (Figures 6B & E). These results were consistent for 20-nm Ag-NPs (Figures 6C & F).
Adipogenic cells were stained for calcium accretion with Alizarin Red S (Figures 7A–C), and lipid accumulation with Oil Red O (Figures 7D–F). Control adipogenic cells did not stain for calcium (Figure 7A) and stained strongly for lipid (Figure 7D). There was no significant change in lipid accumulation or calcium accretion following exposure to 10-nm Ag-NPs at any concentration as evidenced by the continued lack of calcium staining (Figure 7B) and continued strong lipid staining (Figure 7E). Similarly, exposure to 20-nm Ag-NPs at any concentration did not influence the differentiation down the adipogenic pathway, as evidenced by the continued lack of calcium staining (Figure 7C), and continued strong lipid staining (Figure 7F).
Osteogenic cells were stained for calcium accretion with Alizarin Red S (Figures 8A–C), and lipid accumulation with Oil Red O (Figures 8D–F). Control osteogenic cells stained strongly for calcium (Figure 8A) and did not stain for lipid (Figure 8D). There was no significant change in lipid accumulation or calcium accretion following exposure to 10-nm Ag-NPs at any concentration as evidenced by the continued strong calcium staining (Figure 8B) and continued lack of lipid staining (Figure 8E). Similarly, exposure to 20-nm Ag-NPs at any concentration did not influence the differentiation down the osteogenic pathway, as evidenced by the continued strong calcium staining (Figure 8C), and continued lack of lipid staining (Figure 8F).
Bone grafts are the second most transplanted material, second only to blood transfusions . Currently, conventional treatment methods for bone replacement are limited to autografts (grafts derived from the patient), and allografts (grafts derived from a donor). While autografts are the most desirable option due to the significantly reduced immune reaction, patients possess a relative lack of supply. The use of cadaverous allografts provides a larger tissue supply but may cause immunological reactions. Alternatively, hASC are capable of providing patient-specific cells for tissue regeneration therapies due to their high proliferation rates and self-renewal capacity, maintenance of the unspecialized state, migration capability and specialized differentiation into various cell types such as bone, cartilage, fat and muscle. This differentiation may be achieved through chemical induction; however, differentiation may also be influenced by the material properties of the tissue-engineered scaffolds onto which they are seeded.
Every year approximately 300,000 patients who have undergone surgery suffer from surgical-site infection . Studies investigating the effects of surgical-site infection have estimated that an infection increases patient stay by an additional 5 days at a cost of nearly US$18,000 per patient, bringing the yearly cost of surgical-site infection patient care to over $10 billion . Therefore, while the development of tissue engineering of patient-specific bone grafts have become a viable alternative to autografts and allografts, the implantation of these tissue grafts would still suffer from the high rate of surgical-site infection. To overcome this, once an optimal scaffolding material is achieved for each tissue type, antimicrobial activity to prevent infection could be achieved through the incorporation of Ag-NPs. The indiscriminate activity of Ag-NPs and the released ions would provide broad-spectrum antimicrobial activity to scaffolding, and decrease the rate of incidence of infection while improving the success rate and ultimate feasibility of tissue-engineered grafts. In addition, this would help to decrease the widespread use of prophylactic antibiotics that has increased the occurrence of bacterial resistance to typical antibiotics such as methicillin. Therefore, the interaction and metabolism of Ag-NPs with hASC should be minimal for their incorporation into a scaffold to be successful. However, the biocompatibility of Ag-NPs with hASC is a prerequisite to their incorporation into scaffolding. Therefore, this study validated the use of Ag-NP incorporation into a tissue-engineered scaffold by assessing the toxicity, cellular uptake and effect on hASC differentiation following exposure to either 10- or 20-nm Ag-NPs at concentrations of 0.1, 1.0, 10.0, 50.0 and 100.0 μg/ml both prior to, and following, hASC differentiation down their adipogenic and osteogenic pathways.
Fortunately, there are a number of studies that have shown that internalized NPs have no apparent deleterious effects on the morphology, cell proliferation, cell viability and differentiation efficiency of mesenchymal stem cells [9,10]. Studies involving easily functionalized polystyrene and silica NPs and derivatized magnetic NPs used for biomedical imaging, drug delivery and gene therapy have shown that their internalization into hASC does not illicit cytotoxicity [9–11,16]. Multiwalled carbon nanotubes incorporated into tissue engineered scaffolding were not shown to affect the viability or proliferation of hASC . In addition, NPs composed of osteogenic factors have shown remarkable improvements in mesenchymal stem cell adhesion, attachment and differentiation on tissue-engineered bone scaffolds .
The results of this study were similar to our previous research which showed that washed 20-, 50- and 80-nm Ag-NPs did not cause a decrease in viability to human epidermal keratinocytes . This study determined that metallic NPs such as Ag-NPs are capable of interfering with viability assay dye and dye products through the adsorption of cell medium constituents and cytokines, which is a common effect and has been reported for several other viability assays and nanomaterials [19–21]. Based upon these findings, alamarBlue was chosen for this study due to its limited interaction with Ag-NPs. These same Ag-NPs have already been evaluated for their antibacterial efficacy in a previous study, and were found to inhibit the growth of both Gram-positive and Gram-negative bacterial strains such as E. coli, S. aureus, methicillin-resistant S. aureus and Salmonella, beginning at approximately 64 μg/ml. In the same study, AgNO3 was used as a positive control for Ag ions and was shown to inhibit the strains at 1.7 μg/ml, indicating that the 64 μg/ml inhibitory concentration of Ag-NPs released at least an equivalent 1.7 μg/ml of Ag+. Therefore, the concentrations used in the present study were chosen to encompass the bacterial inhibitory concentration .
There is a general agreement that dissolved Ag ions are responsible for the biocidal activity that is especially pronounced against microorganisms, and this ability of Ag-NPs to slowly release these ions from their surface has made them an attractive antimicrobial additive to products. The rate of dissolution is obviously a complicated process that is dependent upon many factors including the method of Ag-NP synthesis, storage length before use, temperature, light exposure, surface functionalization and cell culture conditions . The biological activity of freshly prepared and aged Ag-NPs is remarkably different due to the different amounts of released ions. For example, in a study that utilized hASC as reporter cells to analyze the effect on cell viability and morphology from the release of Ag ions over time from 50 ± 20 nm citrate-stabilized Ag-NPs, it was found that 25 μg/ml of 3-day-old Ag-NPs were enough to cause a decrease in viability to 70%, compared with a complete loss of viability for Ag-NPs first aged in water for 1–6 months . Similarly, 8-nm Ag-NPs in DI water were shown to release less than 0.1 μg/ml of Ag ions after 1 day of incubation and up to 2 μg/ml after 120 days of incubation, while dissolution rates decreased with the addition of citrate stabilization or in the presence of organic matter . In addition, the investigators showed that their release rates were congruent with commercial Ag-NPs stabilized with gelatin and gum Arabic, similar to previous reports [23,24].
Axiomatically, the lethal concentration of Ag-NPs will be higher than that of Ag+ due to the limited release rate of Ag+ from the surface of the particles. The lethal concentration of Ag+ to human cell lines such as germline stem cells, dermal fibroblasts and leukocytes is generally below 5 μg/ml, so it is questionable that many papers report toxicity of Ag-NPs at the same concentration of reported toxicity of Ag+ alone [23–27]. For example, 15-nm Ag-NPs synthesized in a pulsed-plasma reactor have also caused toxicity in germline stem cells at 10 μg/ml . Controversy concerning the concentration of Ag-NP toxicity is most likely due to the Ag-NP synthesis method, whether or not the Ag-NPs are washed, and their length of storage prior to use. Ag-NP solutions may contain residual reducing agent contaminants that are known toxicants, a finding confirmed in this laboratory where the presence of formaldehyde in freshly synthesized Ag-NP solutions was found to be responsible for the toxicity in skin cells compared with thoroughly washed Ag-NPs . The citrate stabilization of the 10- and 20-nm Ag-NPs used in this study may explain their higher lethal concentration, which is congruent with the rare studies that explicitly state that when particles are washed they result in higher lethal concentrations compared with studies that do not mention washing, generally greater than 25 μg/ml [14,22,28,29].
The results of this study demonstrate that exposure of 10- and 20-nm Ag-NPs either prior to differentiation, or following 14 days of hASC differentiation, resulted in no significant cyto-toxicity to hASC, and minimal dose-dependent toxicity to adipogenic and osteogenic cells at 10 μg/ml and greater. Drawing on the results of the previous bacterial study, it is reasonable to conclude that at least 1.7 μg/ml was released from the Ag-NPs at the highest concentration of 100 μg/ml and resulted in increased cell toxicity. In each of the analyses where the hASC were first exposed to Ag-NPs and then differentiated, residual Ag-NPs remained attached to the cells throughout the 14 days of differentiation, which was confirmed by TEM. This is particularly relevant; since degradable tissue-engineered scaffolds containing Ag-NPs will shed these NPs and their ions over the course of the scaffold lifetime to impart their antimicrobial activity, and will therefore interact with the seeded progenitor cells over the course of their differentiation. Each of the progenitor, adipogenic and osteogenic cells showed cellular uptake of both 10- and 20-nm Ag-NPs, without eliciting any abnormal morphological or ultrastructural changes. Lastly, exposure to 10- and 20-nm Ag-NPs for 24 h did not influence the intended differentiation of the undifferentiated hASC, adipogenic or osteogenic cells, and at the antibacterial concentration of 64 μg/ml, the Ag-NPs showed minimal toxicity.
This study showed that exposure of hASC to 10- and 20-nm Ag-NPs either prior to differentiation, or following 14 days of differentiation, resulted in no significant cytotoxicity to undifferentiated hASC. Minimal dose-dependent toxicity was observed for adipogenic and osteogenic cells at concentrations of 10 μg/ml and greater. The cellular uptake of Ag-NPs into each of the hASC, osteocytes and adipocytes did not alter their ultrastructural morphology, or influence hASC differentiation. Exposure of 10- and 20-nm Ag-NPs at concentrations up to 100 μg/ml did not influence hASC differentiation. Although the cell quantity limited this study to the investigation of the effect of Ag-NPs on cell viability, uptake and differentiation, these results conclude that either 10- or 20-nm Ag-NPs are suitable to incorporate into tissue-engineered scaffolds that utilize hASC.
Further studies may be conducted to ensure the biocompatibility of the Ag-NPs with hASC, including assays for hASC immunophenotype preservation or DNA stability, cytokine release, or the effects of multiple Ag-NP exposures during differentiation. These results are promising for future studies where Ag-NPs will be incorporated into tissue-engineered scaffolds. Previously evaluated scaffolding for bone graft therapies comprised of collagen, collagen coated poly(ε-caprolactone) and poly(L-lactic acid)/tricalcium phosphate nanofibers has been shown to increase cell-mediated calcium accretion [30–32], and would be a suitable model to evaluate Ag-NP incorporation. The addition of antimicrobial functionality, namely through the incorporation of Ag-NPs into a tissue-engineered graft scaffold would be pivotal in preventing bacterial growth and thereby minimizing infections, as well as patient and hospital costs.
The authors would like to thank J Hardin (North Carolina State University, NC, USA) for providing assistance with the pooled human adipose-derived stem cells.
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Ethical conduct of research
The authors state that they have obtained appropriate institutional review board approval or have followed the principles outlined in the Declaration of Helsinki for all human or animal experimental investigations. In addition, for investigations involving human subjects, informed consent has been obtained from the participants involved.
Financial & competing interests disclosure
This research was supported by the United States Air Force Office of Scientific Research (USAFOSR) grant FA 9550-08-1-0182 and the NIH (RO1 ES016138). S Oldenburg is the President of nanoComposix (CA, USA). Portions of this article were selected for platform presentation in the Nanotoxicology – Nanosilver Particulates platform session at the 50th Annual Meeting for the National Society of Toxicology (Washington, DC, USA, 8 March 2011). The authors have no other relevant affiliations or financial involvement with any organization or entity with a financial interest in or financial conflict with the subject matter or materials discussed in the manuscript apart from those disclosed.
No writing assistance was utilized in the production of this manuscript.
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