- Open Access
Direct stimulation of human fibroblasts by nCeO2 in vitro is attenuated with an amorphous silica coating
© Davidson et al. 2016
- Received: 8 December 2015
- Accepted: 26 April 2016
- Published: 4 May 2016
Nano-scaled cerium oxide (nCeO2) is used in a variety of applications, including use as a fuel additive, catalyst, and polishing agent, yet potential adverse health effects associated with nCeO2 exposure remain incompletely understood. Given the increasing utility and demand for engineered nanomaterials (ENMs) such as nCeO2, “safety-by-design” approaches are currently being sought, meaning that the physicochemical properties (e.g., size and surface chemistry) of the ENMs are altered in an effort to maximize functionality while minimizing potential toxicity. In vivo studies have shown in a rat model that inhaled nCeO2 deposited deep in the lung and induced fibrosis. However, little is known about how the physicochemical properties of nCeO2, or the coating of the particles with a material such as amorphous silica (aSiO2), may affect the bio-activity of these particles. Thus, we hypothesized that the physicochemical properties of nCeO2 may explain its potential to induce fibrogenesis, and that a nano-thin aSiO2 coating on nCeO2 may counteract that effect.
Primary normal human lung fibroblasts were treated at occupationally relevant doses with nCeO2 that was either left uncoated or was coated with aSiO2 (amsCeO2). Subsequently, fibroblasts were analyzed for known hallmarks of fibrogenesis, including cell proliferation and collagen production, as well as the formation of fibroblastic nodules. The results of this study are consistent with this hypothesis, as we found that nCeO2 directly induced significant production of collagen I and increased cell proliferation in vitro, while amsCeO2 did not. Furthermore, treatment of fibroblasts with nCeO2, but not amsCeO2, significantly induced the formation of fibroblastic nodules, a clear indicator of fibrogenicity. Such in vitro data is consistent with recent in vivo observations using the same nCeO2 nanoparticles and relevant doses. This effect appeared to be mediated through TGFβ signaling since chemical inhibition of the TGFβ receptor abolished these responses.
These results indicate that differences in the physicochemical properties of nCeO2 may alter the fibrogenicity of this material, thus highlighting the potential benefits of “safety-by-design” strategies. In addition, this study provides an efficient in vitro method for testing the fibrogenicity of ENMs that strongly correlates with in vivo findings.
- Cerium oxide nanoparticles
- Engineered nanomaterials
- in vitro dosimetry
Cerium, of the lanthanide metal group, is considered a rare earth metal. Rare earth metals have been reported to induce pneumoconiosis upon occupational exposure, with cerium found to persist in the alveoli and interstitial tissue for decades even after exposure has ceased . Indeed, even the term “cerium pneumoconiosis” has been coined due to the increasing prevalence of such disorders [2, 3]. Use of cerium oxide nanoparticles (nCeO2) has been steadily increasing across many industries, as it is an efficient polishing agent for glass, mirrors, and ophthalmic lenses. In addition, it has been utilized as a diesel fuel catalyst to aid in emission reduction, which subsequently leads to its release in the particulate phase of exhaust [4, 5]. Other uses of nCeO2 in consumer goods are also in development, including use as an additive in cosmetics and sunscreens based on its UV absorption properties, and within the pharmaceutical industry. Thus, human exposure is inevitable in environmental, consumer, and occupational settings, with inhalation being the primary route of exposure.
Unfortunately, data is somewhat limited regarding human exposure concentrations to nCeO2 in either occupational or environmental settings. However, several individual case studies of movie projectionists and photoengravers with regular exposure to nCeO2 have noted the bio-persistence of these particles following occupational exposures, with associated lung disease [6, 7]. Considering the increased demand and use of this material, these reports highlight the need to fully characterize potential exposure-induced health effects associated with nCeO2 use.
Consistent with this notion, several studies have been conducted in an effort to better understand nCeO2-induced effects, with a focus on animal models of disease. These reports have noted the presence of nCeO2-induced pulmonary inflammation, cardiovascular dysfunction, and fibrosis, as well as the bio-accumulation of nCeO2, in agreement with the observed effects reported in human case studies [8–14]. Fibrosis is characterized by the excessive production of extracellular matrix (ECM) components around damaged lung tissue, which accumulate as the typical wound healing response mediated by fibroblasts aberrantly persists . Under normal circumstances, following inflammation or injury, fibroblasts within the lung interstitium produce ECM proteins, such as collagen and fibronectin, in an effort to repair the damaged connective tissue. However, if left unchecked, fibrotic scarring can occur. Unfortunately, very few, if any, therapeutic strategies for the management of fibrosis currently exist, underlying the importance of devising strategies to limit the chances of developing fibrosis in occupational, consumer, and environmental settings.
Given the increasing utility and demand for engineered nanomaterials (ENMs) such as nCeO2, “safety-by-design” approaches are currently being sought in an effort to maximize the functionality of ENMs while minimizing their potential toxicity and adverse health effects. One such strategy is the use of surface coatings, such as a nano-thin amorphous silica (aSiO2) coating, that would provide a biologically inert shell while retaining the desired core material properties when possible . Recent studies using nCeO2 coated with aSiO2 (amsCeO2) have suggested that this approach may prove fruitful, as the coated version of nCeO2 was able to substantially reduce nCeO2-induced pulmonary inflammation, cytotoxicity, phospholipidosis, and fibrosis following acute exposure in rats [9, 17].
While these studies provide critical insight into the utility of this approach for designing safer ENMs, they were completed primarily using in vivo testing models. Given the high number of ENMs in development for countless uses, recently there has been a stronger initiative for more comprehensive in vitro models that would allow for more cost- and time-effective screening tools to identify potential toxicities and hazards associated with the use of these ENMs. Consistently, in the current report we sought to validate the reported in vivo findings that a nano-thin coating of aSiO2 can limit the fibrogenicity of nCeO2 [9, 17] using an in vitro model consisting of primary normal human lung fibroblast (NHLF) cell cultures. Employing the same nCeO2 nanoparticles created using the Harvard Versatile Engineered Nanomaterial Generation System (VENGES), herein we report that nCeO2 can directly stimulate NHLFs, inducing both proliferation and excessive collagen production, both of which are classic hallmarks of fibrogenesis. Furthermore, exposure to nCeO2 significantly induced the formation of fibrotic nodules in cultured NHLFs. In clinical fibrosis, the presence and number of such fibrotic foci is one of the most reliable indicators of a poor prognosis [18–20]. As anticipated, the nano-thin aSiO2 coating limited the fibrogenicity of nCeO2, significantly decreasing the extent of nCeO2-induced fibroblast proliferation, collagen production, and nodule formation, to levels resembling non-treated control cultures. Collectively these results further validate “safety-by-design” strategies for formulating ENMs and offer the details of a reliable in vitro model to analyze fibrogenicity that mimics results observed in vivo.
Preparation and characterization of particle liquid suspensions for cellular studies
Characterization of the engineered nanoparticles
Theoretical aSiO2 (wt%)
400 – 1200
Properties of ENM dispersions in DI H2O and fibroblast growth medium
Intensity-weighted dH (nm)
Volume-weighted dH (nm)
262.5 ± 28.56
0.398 ± 0.03
47.3 ± 6.22
0.0051 ± 0.489
229.7 ± 29.86
0.451 ± 0.11
187.79 ± 16.9
−12.6 ± 2.83
10.7 ± 0.306
222.1 ± 8.86
0.249 ± 0.03
−50.3 ± 2.00
0.0031 ± 6.08e-5
288.3 ± 5.43
0.354 ± 0.02
278.65 ± 11.8
−13.6 ± 0.92
8.00 ± 0.552
132.1 ± 4.45
0.190 ± 0.004
−36.4 ± 3.81
0.0026 ± 1.57e-4
478.9 ± 35.31
0.437 ± 0.05
685.58 ± 263.9
−11.2 ± 2.18
13.0 ± 1.73
Relevant in vitro dose (RID) functions for nCeO2, amsCeO2, and aSiO2 nanoparticles when dispersed in FGM
nCeO2 Low dose
nCeO2 High dose
amsCeO2 Low dose
amsCeO2 High dose
aSiO2 Low dose
aSiO2 High dose
1.10E + 00
1.62E + 06
Interestingly, the observed fibrogenic effects of nCeO2 following a 24 h exposure did reveal a similar trend as the results presented herein that were obtained at the 48 h timepoint (data not shown). Although these results did not reach statistical significance at 24 h post-treatment, these findings highlight the increased fibrogenic potential of the nCeO2 compared to the amsCeO2, since there was roughly 30 % less deposition of the nCeO2 at that time.
nCeO2 induces proliferation and collagen I expression in fibroblasts
As previously mentioned, nCeO2 is known to accumulate in the lungs in both humans and in animal models, and has been found in the pulmonary interstitium long after exposure has ceased [1, 6, 10]. This would suggest that nCeO2 would directly contact resident lung cell types, including fibroblasts. In an effort to determine whether nCeO2 directly stimulates fibroblasts, we measured two hallmarks of fibrosis, cell proliferation and collagen production. Primary human fibroblasts were treated with a low dose, 0.006 μg/cm2, as well as a high dose, 0.2 μg/cm2, which correspond to the physiologically relevant doses that induced pulmonary fibrosis in a rat model [10, 12]. In these in vivo studies, the lowest dose of nCeO2 tested was 0.15 mg/kg body weight. With an average weight of approximately 200 g per rat as noted in the report, this dose translates to approximately 30 μg per animal. Based on the rat lung surface area of 4000 cm2, this corresponds to a dose of approximately 0.0075 μg/cm2, which was sufficient to induce fibrosis at 84 days post-treatment. Using the same calculations, the 3.5 mg/kg dose corresponds to approximately 0.2 μg/cm2, and this dose induced fibrosis 28 days post-treatment [10, 12].
Previous studies from our group have demonstrated that SWCNTs are directly fibrogenic to fibroblast cells, inducing cell proliferation as well as collagen production . Thus, these particles were used as a positive control in the studies reported herein. As expected, SWCNTs also induced cell proliferation at levels similar to both uncoated nCeO2 particles (Fig. 2). Similarly, the known fibrosis-inducing cytokine transforming growth factor beta (TGFβ) was used as a positive control and, as anticipated, invoked a significant level of proliferation in these cells.
nCeO2, but not amsCeO2, induces the formation of fibroblastic nodules
The fibrogenic effect of nCeO2 is mediated by TGFβ signaling
Use of nCeO2 is quickly on the rise worldwide, with an increasing number of applications. Additionally, the increased use as a diesel fuel additive is leading to elevated levels of nCeO2 released in diesel fuel exhaust, further increasing exposure to the general public . Currently, reports of the implications of nCeO2 treatment, both in cell culture models as well as animal models, tend to be conflicting in their determination of whether nCeO2 is hazardous or safe. Indeed, some report the potential efficacy of this compound as a therapeutic agent based on its anti-oxidant and anti-inflammatory properties [30–32]. Still others, such as those discussed within this report, contend that nCeO2 is a potential hazard due to its observed fibrogenicity. This discrepancy seems to be based primarily on the route of exposure, with inhalation being the most hazardous. These results, taken together with reports of nCeO2-induced pulmonary disease and fibrosis following inhalation exposure [5, 6, 10, 12], raise public health concerns due to the fact that most current applications of nCeO2 employed have the ability to generate respirable particles.
The potential health hazards caused by exposure to ENMs such as nCeO2 has led to the development of alternative engineering methods to create safer materials while still maintaining the desirable characteristics of the material, commonly referred to as “safety-by-design” strategies. One such method employs a nano-thin layer of amorphous silica to “mask” the outside of the particle, since amorphous silica is considered to be relatively biologically inert [16, 33]. One main concern with these types of strategies is that the core material will no longer possess its desired properties once encapsulated. Indeed, in the case of CeO2, the desirable catalytic properties may not be retained with an aSiO2 coating; thus, depending on the application, this strategy may not always prove fruitful. However, when considering the observed results obtained in rat models, that amsCeO2 causes less acute inflammation and pulmonary cell toxicity as compared to the uncoated nCeO2, and minimizes markers of fibrosis such as the accumulation of surfactant in the air space and collagen production [9, 17], it seems that this strategy is worth pursuing when the application would tolerate such coatings. Consistent with this notion, nano-thin aSiO2 coating also demonstrated a protective effect when used to encapsulate iron oxide, reducing both toxicity and genotoxic effects in two different cell types . Collectively these reports, as well as the results demonstrated herein, validate this concept of “safety-by-design” for ENMs for further study and development.
As previously mentioned, current reports focused on nCeO2 provide conflicting notions regarding the safety or potential toxicity of this nanoparticle. While some of these discrepancies can be attributed to the method of exposure, such as ingestion versus inhalation, others may be more attributable to differences in the toxicological experimental methods employed (e.g., dosing, timing, dispersion method, measured outcome). Unfortunately, there is limited data on actual human exposure concentrations to nCeO2, and this makes predicting physiologically relevant doses somewhat difficult for experimental investigation. Likewise, nanoparticles are known to behave differently in various types of cell culture or dispersion media, often due to effects like the formation of protein coronas which can alter the bio-interactions of these particles once delivered to cells [17, 35, 36]. Several in vitro studies have examined the potential toxicity of nCeO2, using numerous cell lines and endpoints, and most have concluded that nCeO2 is relatively non-toxic and does not illicit a strong inflammatory response [17, 37–40]. On the contrary, when investigated in vivo, nCeO2 has demonstrated both pro-inflammatory and pro-fibrogenic properties [8–10, 12, 14, 17, 41], which seems more consistent with the reported health effects observed in human case studies .
These apparent disparities between in vitro and in vivo results make evaluating the potential hazards of nCeO2 difficult, and highlight the need for further development of more reliable and consistent in vitro models to study and predict the fibrogenicity potential of ENMs. This is especially important when considering the fact that animal studies can be time-consuming, costly, and limited in terms of high-throughput potential when screening a large number and variety of particles. Given the vast number of ENMs in use and in development, a number that continues to grow daily, this notion seems more critical than ever. Furthermore, in vitro cell models are useful in allowing more in depth analysis of the specific mechanisms employed by certain cell types as a result of exposure that cannot be assessed in vivo due to the complexity of the entire system. These mechanistic details can provide vital evidence that may be utilized for the purpose of developing therapeutic and diagnostic strategies or outcomes. For example, our model allowed us to utilize the TGFβ inhibitor SB431542 to investigate the extent to which TGFβ signaling plays a role in nCeO2-induced fibrogenicity specifically in fibroblast cells, which we would not have been able to accomplish in vivo (Fig. 6). In vivo models will always remain a necessary approach to predict human response and potential disease outcomes, however, development of more novel, reliable in vitro methods would be extremely advantageous in helping to identify select agents that should be fully characterized using in vivo approaches.
In light of these concerns, we sought to develop a reliable in vitro model to examine the potential fibrogenicity of nCeO2 using primary human fibroblasts. These cells present a desirable cell type for in vitro analysis of nCeO2 since this particle is known to persist in the lung and has been found in the interstitium [1, 6, 10, 27–29]. Furthermore, in vivo models suggest that the primary negative outcome of exposure to nCeO2 is fibrosis, which lends to the notion that fibroblast cells may be the main cell type involved in the biological response to nCeO2. Thus, we directly treated primary human fibroblasts with nCeO2 or amsCeO2 to assess fibrogenicity. Our group has also previously employed this strategy to evaluate nanomaterials, specifically carbon nanotubes, and found that this model consistently correlated with in vivo outcomes [21, 42]. In the current report, we observed increased markers of fibrogenicity, cell proliferation, and collagen production (Figs. 2 and 3) when NHLFs were directly treated with nCeO2 at physiologically relevant doses that match those reported in vivo [9, 10, 12]. nCeO2 is relatively insoluble under typical cell culture conditions , indicating that the effects reported here are likely due to cellular interactions with particulate nCeO2 rather than dissolved cerium. In addition, we saw a significant increase in the formation of fibrotic foci when the cells were treated with nCeO2 (Fig. 4). These findings demonstrate that this in vitro model was able to accurately mimic results obtained using in vivo models [9, 10, 12, 17]. Similarly, our results accurately portrayed the observed in vivo effects of the nano-thin amorphous silica coating of nCeO2 when exposed to the NHLF cells, showing cell proliferation, collagen expression, and fibrotic nodule formation at levels consistent with non-treated and negative controls. These results also further validate the “safety-by-design” approach for further development of ENMs.
As mentioned, the higher dose of nCeO2, 0.2 μg/cm2, employed in our studies is equivalent, based on body weight and surface area of the rat lung, to the physiologically relevant dose that has been used in numerous in vivo models to initiate fibrosis. Indeed, using this dose we also observed the correlative fibrogenic potential of nCeO2 in our in vitro model. Interestingly, the low dose of 0.006 μg/cm2 used in these studies, which scarcely induces fibrosis in vivo, also induced a significant fibrogenic effect in our model. These results are noteworthy since they indicate that even very low levels of exposure may have the potential to initiate a fibrotic response. This is especially important in the case of nanomaterials when considering their bio-persistence. In addition, this finding highlights the notion that reliable in vitro models may be useful in identifying potentially harmful doses of materials that would be relevant for follow up using in vivo models. Indeed, it plausible that interstitial fibroblasts would be exposed to lower doses of inhaled nanoparticles than other cell types of the lungs following exposure, due to factors such as clearance as well as translocation rate into the interstitium.
In summary, the results presented herein demonstrate that treatment of primary human lung fibroblasts in vitro is a useful approach for evaluating the potential fibrogenicity of nanomaterials that can efficiently represent results obtained in vivo. Furthermore, our results confirm those obtained using an in vivo rat model that a nano-thin coating of amorphous silica on the surface of nCeO2 can successfully ameliorate the fibrogenicity of this nanomaterial. These results not only support the notion that “safety-by-design” strategies for developing ENMs are useful, but also demonstrate the utility of the current in vitro model for testing the fibrogenic potential of respirable nanoparticles.
Reagents and antibodies
Fibroblast basal medium, growth supplements, and NHLFs were purchased from Lonza (Walkersville, MD). Human-derived transforming growth factor beta (TGFβ), as well as the TGFβ receptor blocker SB431542, was obtained from R&D Systems, Inc. (Minneapolis, MN). Poly-L-lysine was purchased from Sigma-Aldrich (St. Louis, MO). The anti-Collagen I antibody was purchased from Fitzgerald (Acton, MA), while the alpha tubulin antibody was purchased from Santa Cruz Biotechnology, Inc. (Dallas, TX). Alexa-fluor 488-conjugated donkey anti-rabbit secondary antibody, alexa-fluor 488-conjugated alpha-smooth muscle actin (α-SMA) primary antibody, and the beta actin primary antibody were purchased from Abcam (Cambridge, MA). ProLong gold antifade with DAPI mountant was obtained from Molecular Probes (Thermo Fisher Scientific, Waltham, MA).
Particle generation and characterization
Nano-scaled CeO2, amsCeO2, and aSiO2 particles were generated using the Harvard Versatile Engineered Nanomaterial Generation System (VENGES) and characterized as previously described . Briefly, x-ray diffraction (XRD) patterns were obtained using a Scintag XDS2000 powder diffractometer [Cu Kα (λ = 0.154 nm), −40 kV, 40 mA, stepsize = 0.02°]. The crystal size was determined by applying the Sherrer Shape Equation to the Gaussian fit of the major diffraction peak. The Brunauer–Emmett–Teller (BET) powder-specific surface area (SSA) of all samples was measured by nitrogen adsorption at 77 K (Micromeritics TriStar; Norcross, GA), after sample degassing for 1 h at 150 °C in nitrogen. BET equivalent primary particle size was calculated, under a spherical particle assumption, using dBET = 6000/(ρ × SSA), where ρ is the material density.
Dry nCeO2, amsCeO2, and aSiO2 particle dispersions in complete fibroblast growth medium (FGM) were prepared using a protocol developed by the authors , in which the particle-specific critical delivered sonication energy (DSEcr), hydrodynamic diameter (dH), formed agglomerate size distribution, polydispersity index (PdI), zeta potential (ζ), specific conductance (σ), pH, colloidal stability, and effective density of formed agglomerates are measured . For treatment of cell cultures, particles were suspended in DI H2O to acquire stock solutions of 0.1 mg/mL. Immediately prior to use, all particles were dispersed via sonication and subsequently diluted in FGM to the desired concentrations. Particles were then briefly vortexed and slowly added to the cultures.
Subsequent to particle suspension, preparation, and characterization, the delivered-to-cell mass was calculated. Unlike soluble chemicals, colloidal suspensions of nanoparticles can have altered surface area, agglomerate formation, and settling rates depending on the suspension media, which may impact the bio-interactions of the particles when deposited onto cells in culture. Thus, dosimetric considerations must be taken into account. Therefore, the fraction of administered particle mass that is deposited on the cells as a function of in vitro exposure time (fD) was calculated [22, 44] in order to accurately replicate the in vivo lung deposited doses of nCeO2 [9, 10, 12]. The fD as a function of in vitro exposure time was calculated using the hybrid Volumetric Centrifugation Method-In Vivo Sedimentation, Diffusion and Dosimetry (VCM-ISDD) methodology [22, 44, 45] developed by the authors. The mean media-formed volume-weighted agglomerate hydrodynamic diameter (dH) and the VCM-measured effective density of formed agglomerates  were used as inputs to the VCM-ISDD fate and transport numerical model in order to estimate the fD as a function of time.
Preparation of carbon nanotubes
Single-walled carbon nanotubes (SWCNT; Carbon Nanotechnologies, Inc., Houston, TX) were produced by the high pressure CO disproportionation (HipCo) technique, using CO in a continuous-flow gas phase as the carbon feedstock and Fe (CO)5 as the iron-containing catalyst precursor. The SWCNTs were subsequently purified by acid treatment to remove metal contaminants. Nitric acid dissolution and inductively coupled plasma-atomic emission spectrometry (ICP-AES, NMAM #7300) were used to perform an elemental analysis of the supplied SWCNTs, and indicated that they contained 99 % elemental carbon and 0.23 % iron. The specific surface area was measured at −196 °C by the nitrogen absorption-desorption technique (BET) using a SA3100 Surface Area and Pore Size Analyzer (Beckman Coulter, Fullerton, CA). The surface area of dry SWCNT was 400 – 1,000 m2/g, and the length and width of individual (dry) SWCNT was 0.1 – 1 μm and 0.8 – 1.2 nm, respectively.
Dry SWCNTs were prepared for treatment as previously described and validated . Briefly, particles were suspended in distilled water to acquire stock solutions of 0.1 mg/mL, which were supplemented subsequently with 150 μg/mL of a natural lung surfactant, Survanta (Abbott Laboratories, Columbus, OH) to aid in their dispersion. All particles were then dispersed using brief sonication and diluted in culture medium to the desired concentration.
NHLFs were obtained from Lonza (Walkersville, MD) and cultured in FGM, which is composed of Fibroblast Cell Basal Medium (FBM; Lonza) that contains all recommended growth supplements (FGM™-2 BulletKit™; Lonza). Cells were cultured and maintained at sub-confluent densities in a humidified incubator at 37 °C with 5 % CO2. For each experiment, cells were seeded at density of 2.5 ×104 cells per well in a 24-well plate the day before treatments were performed.
Cells were seeded at a density of 2.5 × 104 cells per well onto glass coverslips that had been treated with poly-L-lysine (0.1 μg/mL), rinsed, and dried. Prior to their addition to cells, stock solutions of nanoparticles were sonicated and subsequently diluted in FGM to the desired concentration. Treated fibroblasts were incubated with nanoparticles for 48 h and were then fixed in 4 % paraformaldehyde and permeabilized using phosphate buffered saline containing 0.25 % Triton-X 100. Cells were then blocked with 2 % normal donkey serum and incubated with primary antibody raised against collagen I, followed by fluorescently conjugated secondary antibody. Cover glasses were then mounted on glass slides using ProLong Gold Antifade mountant with DAPI. Fluorescent and brightfield images were captured using a Zeiss Axiovert 100 TV inverted microscope (Carl Zeiss Microscopy, LLC, Thornwood, NY). For CytoViva images, coverslips were mounted onto laser-cut glass slides and images were captured using an Olympus BX-51 Microscope equipped with the CytoViva Advanced Dark field Illumination System (CytoViva, Auburn, AL) and a 100 W quartz-halogen light source.
Alternatively, cells stained for α-SMA were plated into chamber slides (Nalgene Nunc International, Naperville, IL) at a density of 1 ×104 cells per well. Stock solutions of nanoparticles were sonicated and subsequently diluted in FGM to the desired concentration for cell treatment. Fibroblasts were incubated with nanoparticles for 48 h and cells were then fixed with 4 % paraformaldehyde in PBS solution on ice for 30 min and permeabilized with 2 % Triton-X 100 for 30 min at room temperature. After washing, cells were blocked with normal rabbit serum for 1 h and then incubated overnight at 4 °C with primary antibody raised against α-SMA that was conjugated with alexa-fluor 488. Cells were then washed and mounted with mounting solution containing DAPI (Vector Laboratories, Inc., Burlingame, CA). Images were taken using a Nikon Ti Eclipse fluorescent microscope.
Cell proliferation determination
Fibroblast cells were prepared, treated, and imaged as described for immunofluorescence. Resultant images were then analyzed for total cell numbers via Image J software (Bethesda, MD) by counting the total number of DAPI stained nuclei per 10X field. Four fields were captured per coverslip in duplicate for each of three independent replicates.
Immunoblot analysis and collagen I quantification
Following treatment, whole cell lysates were collected using cell extraction buffer (Life Technologies, Thermo Fisher Scientific, Waltham, MA) supplemented with 0.1 mM PMSF and a mixture of protease and phosphatase inhibitors. Cellular debris was removed by high-speed centrifugation and protein concentrations were then determined in each sample using the Pierce BCA Protein Assay (Life Technologies, Thermo Fisher Scientific, Waltham, MA). Samples (25 μg protein/lane) were separated on sodium dodecyl sulfate (SDS)-polyacrylamide gels and electrophoretically transferred to nitrocellulose membranes. The membranes were then analyzed with collagen I, beta actin, or alpha tubulin primary antibodies, and bound antibodies were detected using HRP-conjugated secondary antibodies. Densitometry was performed on the resulting bands using Image J software (NIH, Bethesda, MD) to quantitate the protein concentration in each sample.
Fibroblastic nodule assay
NHLFs were seeded onto glass coverslips that had been treated with poly-L-lysine (0.1 μg/mL) at a density of 2.5 ×104 cells per well in a 24 well plate, and allowed to adhere overnight. Prior to their addition to cells, nanoparticles were sonicated using a cup sonicator and were diluted in FGM to the desired concentration. For experiments employing the TGFβ inhibitor SB431542, cells were incubated with 1 μM of the inhibitor for 3 h prior to addition of the nanoparticles. Fibroblasts were then incubated with nanoparticles for 48 h and were subsequently fixed in 4 % paraformaldehyde and permeabilized using phosphate buffered saline containing 0.25 % Triton-X 100. Cells were then blocked with 2 % normal donkey serum and incubated with primary antibody raised against collagen I, followed by fluorescently conjugated secondary antibody. Cover glasses were then slowly washed and subsequently mounted on glass slides using ProLong Gold Antifade mountant with DAPI. Fluorescent and brightfield Images were captured using a Zeiss Axiovert 100 TV inverted microscope (Carl Zeiss Microscopy, LLC, Thornwood, NY). Confocal microscopy z-stack images were obtained using a Zeiss LSM780 confocal microscope. For each culture, two cover slides were analyzed and counted for nodule formation and data was pooled from three independent replicates.
Data represents mean ± SEM from three or more independent replicates and samples were analyzed using a one-way ANOVA with Tukey’s post-test for multiple comparisons to determine significance. Statistical significance is indicated in each figure as *p < 0.05, **p < 0.01, and ***p < 0.001. All statistical analyses were performed using GraphPad Prism Software (La Jolla, CA).
The authors would like to thank Mark Barger and Dr. Jane Ma for their kind assistance with the study. This work was supported by the National Institute for Occupational Safety and Health, Nanotechnology Research Center Fund, and the National Science Foundation grants number 1235806 and 1434503.
The findings and conclusions in this report are those of the authors and do not necessarily represent the views of the National Institute for Occupational Safety and Health.
Use of brand name does not constitute product support.
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