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The past decade has seen significant increases in combustion-generated ambient particles, which contain a nanosized fraction (less than 100 nm), and even greater increases have occurred in engineered nanoparticles (NPs) propelled by the booming nanotechnology industry. Although inhalation of these particulates has become a public health concern, human health effects and mechanisms of action for NPs are not well understood. Focusing on the human airway smooth muscle cell, here we show that the cellular mechanical function is altered by particulate exposure in a manner that is dependent upon particle material, size and dose. We used Alamar Blue assay to measure cell viability and optical magnetic twisting cytometry to measure cell stiffness and agonist-induced contractility. The eight particle species fell into four categories, based on their respective effect on cell viability and on mechanical function. Cell viability was impaired and cell contractility was decreased by (i) zinc oxide (40–100 nm and less than 44 μm) and copper(II) oxide (less than 50 nm); cell contractility was decreased by (ii) fluorescent polystyrene spheres (40 nm), increased by (iii) welding fumes and unchanged by (iv) diesel exhaust particles, titanium dioxide (25 nm) and copper(II) oxide (less than 5 μm), although in none of these cases was cell viability impaired. Treatment with hydrogen peroxide up to 500 μM did not alter viability or cell mechanics, suggesting that the particle effects are unlikely to be mediated by particle-generated reactive oxygen species. Our results highlight the susceptibility of cellular mechanical function to particulate exposures and suggest that direct exposure of the airway smooth muscle cells to particulates may initiate or aggravate respiratory diseases.
The very large internal surface area of the lungs, approximately 150 m2 (Gehr et al. 1978), is continuously exposed to both innocuous and harmful particulates. These particulates are dealt with by macrophage clearance, the mucociliary escalator and a series of structural and functional barriers (Nicod 2005). Despite the existence of these defences, respiratory diseases are frequent and increasing (Peters et al. 1997; Wichmann et al. 2000; Schulz et al. 2005; Pope et al. 2009). Moreover, numerous epidemiological studies have established a causal link between exposure to ambient particulate matter and increased pulmonary and cardiovascular morbidity and mortality (Pope et al. 1995; Peters et al. 1997, 2001; Lighty et al. 2000; Penttinen et al. 2001; Dockery et al. 2005; Schulz et al. 2005; Weichenthal et al. 2007).
These findings raise the important question of how and over what time scale particulates evade host defences. Consistent with the ability of nanoparticles (NPs), but not micrometre-sized particles (MPs), to penetrate through the submicrometre-thick air–blood barrier (Gehr et al. 1978; Geiser et al. 2005), recent studies indicate a potential toxic risk of inhaled NPs, mainly combustion-derived particles smaller than 0.1 μm in diameter (Borm & Kreyling 2004; Araujo et al. 2008). A new source for airborne NPs is associated with the booming nanotechnology industry and its many related products, especially engineered NPs (Mazzola 2003; Paull et al. 2003). Nonetheless, the ability of engineered NPs to cause adverse health effects following accidental or occupational exposure is not well understood (Maynard et al. 2006).
The deposition and clearance of particles in the lung are particle-size dependent. Data and computer models suggest that while large (greater than 1 μm) and very small (less than 2 nm) particles tend to deposit in the nasopharyngeal compartment, intermediate-sized NPs (2–100 nm) exhibit significant deposition in the alveolar and tracheobronchial compartments (Oberdorster et al. 2005). The deeper the particles are deposited in the lung, the longer it takes to clear them and the higher is the probability of adverse health effects owing to particle–tissue and particle–cell interactions (Rothen-Rutishauser et al. 2009). Adverse health effects may also be caused by NPs penetrating into the capillary blood and subsequent translocation into other organs (Kreyling et al. 2002; Geiser et al. 2005; Muhlfeld et al. 2007). There, NPs may alter the organ function through direct interaction with key cell types. In vitro studies using cell cultures are providing mechanistic insights into the action of NPs on neurons (Pisanic et al. 2007), epithelial cells, macrophages, dendritic cells (Rothen-Rutishauser et al. 2005, 2007, 2008) and cardiac muscle cells (Helfenstein et al. 2008). Owing to its proximity to the lung epithelium, the airway smooth muscle cell is susceptible to direct exposure to NPs; this indeed has been observed in human biopsy (Pinkerton et al. 2000; Churg et al. 2003). Nonetheless, the airway smooth muscle cell has received little attention, even though its altered contractile and relaxing responses are intimately related to airway hyper-responsiveness, asthma and other respiratory diseases (Bai 1990; Fredberg et al. 1996; Shore 2004; An et al. 2006).
In this paper we focus on the human airway smooth muscle (HASM) cell and investigate the effects of eight particle species on the HASM cell's contractile and relaxing responses to biochemical agonists using optical magnetic twisting cytometry (OMTC; Fabry et al. 2001a; Bursac et al. 2005; Deng et al. 2006; Trepat et al. 2007; Zhou et al. 2009). We compared the particulate effect of six different materials: two combustion-derived polydisperse particles included welding fumes (WF) and diesel exhaust particles (DEPs), both of which have significant nanosized fractions (Donaldson et al. 2005); engineered NPs included titanium dioxide (TiO2), fluorescent polystyrene spheres (FS), zinc oxide (ZnO) and copper(II) oxide (CuO). We also assessed the particle-size effect by comparing the ZnO and CuO NPs with their micrometre-sized counterparts. The particles fell into four categories, based on their respective effect on cell viability and on mechanical function. Importantly, we demonstrate that particles could alter cell mechanics dose dependently with little or no concomitant change in cell viability.
HASM cells were maintained in Ham's Nutrient Mixture F-12 medium supplemented with 10 per cent foetal bovine serum (FBS), 100 U ml−1 penicillin, 100 μg ml−1 streptomycin, 200 μg ml−1 amphotericin B, 12 mM NaOH, 1.6 mM CaCl2, 2 mM l-glutamine and 25 mM HEPES. We plated cells (passages 5–7) in collagen I-coated 96-well plastic plates (Corning, Corning, NY, USA) at 20 000 cells per well and waited 4–6 days before switching the serum-containing media to serum-free media supplemented with insulin (5.7 μg ml−1) and transferrin (5 μg ml−1) (IT media). After 24 h of serum deprivation, we started the treatment with either particles or chemicals, both of which were suspended or dissolved in the IT media. Since we added 0.2 ml media per well, a particle dosage of 1 μg ml−1 is equivalent to 0.625 μg cm−2. This treatment lasted for 16–22 h before biomechanical or biochemical measurements. We also tested the effect of hydrogen peroxide (H2O2) and zinc chloride (ZnCl2; Sigma-Aldrich), following the same procedure as with particles.
Eight particle species were used: DEP (SRM 2975 from National Institute of Standards and Technology, USA), WF (0.92–1.38 μm; metal arc welding using mild steel; Antonini et al. 1999), TiO2 (25 nm; Aeroxide from Evonik Degussa Corporation, NJ, USA), FS (40 nm; carboxylate-modified polystyrene FluoSpheres, Invitrogen), CuO5 μm (less than 5 μm; Sigma-Aldrich), CuO50 nm (less than 50 nm; Sigma-Aldrich), ZnO40 nm (40–100 nm; Alfa Aesar) and ZnO44 μm (less than 44 μm; Alfa Aesar). Particles were weighed (except for FS, which was suspended in water and pipetted) and suspended directly in the IT media at 10 mg ml−1. The suspensions were sonicated for 20–30 s using a sonicator (Sonifier Cell Disruptor, model no. W200P, Heat systems-ultrasonics Inc., Plainview) right before adding to cells. We always prepared fresh particle suspensions right before the treatment.
OMTC is a high-throughput tool for quantifying adherent cell mechanics with remarkable temporal and spatial resolution (Fabry et al. 2001b). Briefly, we produced 4.5 μm ferromagnetic beads and coated them with poly-l-lysine (PLL; 4 kDa) at 75 μg PLL per mg beads. This coating allows avid binding to cell surface and has been shown to give similar cell stiffness measurements compared with coating with RGD peptides (Bursac et al. 2007; Zhou et al. 2009). However, PLL does not induce integrin clustering and focal adhesion formation, as RGD does; therefore, the passive binding of PLL will cause less alteration in the cell to be measured. PLL offers the additional advantages of better storage stability and dispersion of the coated beads. After overnight particle suspension treatment, we replaced cell media with fresh IT media, thus removing any suspended or loosely bound particles. After 20 min, the coated beads were added and allowed to incubate with the cells for 20–40 min before OMTC measurements; this variability in bead incubation time had little effect on the measured cell stiffness. To measure cell stiffness, the beads were first magnetized horizontally by a large magnetic field; each bead became a small magnet (M). A much weaker magnetic field oscillating at 0.77 Hz (H) was then applied vertically, which applied a sinusoidal torque to the beads. Motion of the beads (d) was optically recorded (figure 1a). The ratio between the torque and bead motion thus defined an apparent stiffness for a cell, which had the unit Pa nm−1. In a typical run, we would start the twisting field to continuously monitor cell stiffness for a few hundred cells, add histamine (100 µM) or isoproterenol (100 µM), both from Sigma-Aldrich, at 50 s and continue twisting for another 5 min. This would allow us to obtain three quantities, the stiffness prior to applying agonist (G0), the maximum response to isoproterenol (R) and the maximum response to histamine (C); the latter two are illustrated in figure 1b. All measurements were performed at 37°C. Custom software was written in Matlab to automate the large-volume data analysis.
The measurement of cell stiffness, contractile response and relaxing response using OMTC. (a) The working mechanism of OMTC. The magnetized bead (M) is twisted by the vertical magnetic field (H); the lateral motion of the bead (d) is inversely related ...
We determined cell viability using Alamar Blue (Invitrogen). Cells were cultured and treated with particles using the same procedure as for OMTC assay, with the same number of cells per well. Alamar Blue was added to each well at 10 per cent volume and incubated for 200 min. Metabolically active cells reduce the dye into a fluorescent form, and this fluorescent emission signal was measured using a plate reader (excitation/emission: 544 nm/590 nm; Fluoroskan Ascent Plate Reader, ThermoFisher). The emission signal was used to estimate cell viability by linear interpolation between the emission from cells treated with 0.1 per cent saponin (0% viability) and that from untreated cells (100% viability). We compensated for the possible interference of particles with the Alamar Blue assay using the procedure below.
To test whether the presence of particles interferes with this fluorescence-based assay, we performed a cell-free experiment. We first incubated IT media containing 10 per cent Alamar Blue with fully confluent, untreated HASM cells in culture flasks for 200 min; the fully reduced media then represent 100 per cent viability. These media were collected and particles added to them at the same doses as in cell treatments. We loaded the particle suspensions, together with positive control (fully reduced media with no particle) and negative control (IT with 10% fresh Alamar Blue), in a 96-well plate, incubated overnight in a cell culture incubator and read the fluorescence the next day. This incubation mimics the procedure for cell treatment, during which the particles partially sediment. Using linear interpolation between negative control and positive control, we can estimate a nominal viability. Since our cell-free assay defined the emission signal for 100 per cent viability for all particles at all doses, we can use this nominal viability to compensate for any artefact introduced by the presence of the particles, by normalization.
For the OMTC assay, statistical comparisons with no-particle control were made using the Kruskal–Wallis non-parametric one-way analysis of variance by ranks. For the cell viability assay, statistical comparisons with no-particle control were made using Student's t-test with two tails and unequal variance. A difference was considered significant if p ≤ 0.01. We list all the sample sizes in the electronic supplementary material, table S1, for OMTC assay and in the electronic supplementary material, table S2, for the Alamar Blue assay; each experiment was repeated at least once on a different day. For OMTC assay, we report the median with standard errors; for cell viability indices, we report the mean with standard errors. We note that the error bars are often so small that they are masked by the data symbol.
The results are presented first with respect to viability over all particulate species. This is followed by the results for cell mechanics. We conclude this section by exploring the role of reactive oxygen species (ROS).
In contrast to the claim that the Alamar Blue assay is not affected by particulates (Fahmy & Cormier 2009), our cell-free experiment demonstrated that some particles can interfere with this assay. FS (polystyrene NPs) and TiO2 dose dependently increased the nominal viability by up to 20 per cent at 200 μg ml−1; whereas CuO50 nm and DEPs dose dependently decreased the nominal viability by up to 19 and 16 per cent, respectively, at 200 μg ml−1 (electronic supplementary material, figure S1, left). The other particles did not interfere with the Alamar Blue assay. The raw Alamar Blue data for particle-treated cells are shown in the electronic supplementary material, figure S1, right, in which FS and TiO2 artificially caused a dose dependent increase in viability beyond 100 per cent. To compensate for the artefacts introduced by the presence of the particles, we normalized the raw Alamar Blue viability with the nominal viability that we measured in the absence of cells with the same particle species and dose.
Up to 200 μg ml−1, TiO2, DEP, FS and WF did not decrease cell viability by more than 20 per cent (figure 2a). While consistent with independent findings on TiO2 and DEP (Lehmann et al. 2009; Müller et al. 2009), these findings differed from those of others on FS toxicity on rat lung macrophages (Frohlich et al. 2009) and on WF toxicity on a human endothelial cell line (Antonini et al. 1999). Better controlled experiments are needed to determine whether HASM cells are more tolerant of these two particles than those other cell types.
The effect of eight particles on the viability of HASM cells after correcting for the optical interference of particles. (a) At the doses tested, TiO2, DEP, FS and WF caused little change in cell viability. (b) CuO NPs, but not MPs, caused dose-dependent ...
ZnO was remarkably toxic for HASM cells, with significant but relatively small dependence on particle size (figure 2c). With nearly 1000-fold difference in size, the 50 per cent lethal dose (LD50) for ZnO44 μm is only 49 per cent higher than that for ZnO40 nm (table 1), presumably owing to a slower dissolution rate for the former. Furthermore, ZnO40 nm exhibited toxicity similar to that of soluble ZnCl2 at the same zinc concentration (figure 2c). This suggests that the toxicity for these particles is largely a consequence of soluble Zn2+, consistent with the considerable solubility of ZnO (Xia et al. 2008). Thus, while essential for a wide range of biochemical reactions, excess zinc can impair cell physiology (Dineley et al. 2003; Sharpley & Hirst 2006; Gazaryan et al. 2007).
Interestingly, CuO particles exhibited size-dependent toxicity. CuO NPs decreased cell viability dose dependently with an LD50 of 186.4 μg ml−1; by contrast, the MPs did not alter cell viability (figure 2a and table 1). This finding is consistent with a previous report (Karlsson et al. 2009).
Having determined toxicity of the various particles as a function of species and size, we quantified the changes in the mechanical functions of the HASM cell following particulate exposure. For these functional assays, we employed much lower concentrations where the viability is decreased by no more than 10 per cent, except for ZnO particles. Up to 50 μg ml−1, TiO2 and DEP altered the cell stiffness, contraction induced by histamine and relaxation induced by isoproterenol by no more than 50 per cent; these alterations exhibited no clear dose dependence (figure 3). The moderate effect of TiO2 and DEP we observed here is consistent with their moderate effects on cardiomyocyte electrophysiology (Helfenstein et al. 2008).
TiO2 and DEP caused minor changes in (a) cell stiffness, (b) contractile response induced by histamine and (c) relaxing response induced by isoproterenol. All indices have been normalized to those of untreated cells. Lines with open circles, TiO2; lines ...
Exposure to ZnO elicited a different response. At doses below 5 μg ml−1, the intrinsic stiffness and isoproterenol response changed little, while histamine response increased moderately (figure 4a–c). However, at 7 μg ml−1, all three indices nearly vanished for ZnO40 nm; the same occurred for ZnO44 μm-treated cells at 10 μg ml−1 (figure 4a–c). Consistent with cell viability assay, the OMTC assay suggested that the ZnO NPs are moderately more effective at impairing the biomechanical function than the MPs. To quantitatively compare the viability assay and the biomechanical assay, we looked at the effective doses for 50 per cent inhibition (ED50) and LD50 (table 1). For each ZnO particle, the ED50 and LD50 are quite comparable. This suggests that a cytotoxicity mechanism accounts for both the loss of viability and the impairment of cell mechanics, presumably through depletion of ATP (Dineley et al. 2003).
ZnO NPs and MPs caused dose-dependent inhibition of (a) cell stiffness, (b) contractile response and (c) relaxing response. Lines with open triangles, ZnO44 μm; lines with filled triangles, ZnO40 nm.
Despite the fact that Cu2+ and Zn2+ ions are both divalent, the CuO particles differ fundamentally from ZnO in their effects on HASM cells. CuO MPs are much less toxic than CuO NPs, as shown above. Our OMTC assay further revealed little change in the cell stiffness (figure 5a), contraction (figure 5b) or relaxation (figure 5c) with the cells exposed to up to 50 μg ml−1 MPs. By contrast, the NPs caused a dramatic dose-dependent decrease in all three indices, with nearly 100 per cent inhibition at 50 μg ml−1 (figure 5). At this dose, the Alamar Blue assay revealed only 7 per cent decrease in viability; consistently, LD50 was five times higher than ED50 (table 1). Thus, unlike ZnO, CuO NPs could inhibit cell stiffness and contractility with minimal impairment of viability.
CuO NPs, but not MPs, caused dose-dependent inhibition of (a) cell stiffness, (b) contractile response and (c) relaxing response. Lines with open squares, CuO5 μm; lines with filled squares, CuO50 nm.
Exposure of particles to other species also showed that cell mechanics could be altered without affecting viability. FS particles of 40 nm induced a dose-dependent inhibition of stiffness, contraction and relaxation of the HASM cells (figure 6). By contrast, while it did not affect cell stiffness or relaxation, WF greatly enhanced cell contraction in response to histamine (figure 6). These data suggest direct particulate exposure can markedly alter the mechanical properties and function of the HASM cell.
FS and WF changed cell mechanics in opposite ways. FS dose dependently inhibited (a) stiffness, (b) contraction and (c) relaxation. By contrast, WF had little effect on (a) stiffness or (c) relaxation, but (b) dose dependently enhanced contractile response ...
What are the mechanisms of action responsible for the diverse changes in cellular viability and mechanics? While detailed biochemical analysis is beyond the scope of the current work, we addressed the potential role of ROS in mediating these changes. ROS are known to be induced by a wide range of particulates and are therefore a candidate pathway leading to NP toxicity (Xia et al. 2006). We subjected the HASM cells to ROS by exposure to H2O2. Surprisingly, with doses up to 500 μM, H2O2 caused no change in viability and did not alter the HASM cell stiffness, contraction or relaxation (electronic supplementary material, figure S2). To rule out the possibility that the H2O2 dosage was inaccurate owing to storage, we repeated the cell viability assay using newly purchased H2O2 solution and obtained identical results: LD50 for H2O2 was 1116 μM (electronic supplementary material, figure S2d). Our finding of the high tolerance of HASM cells to H2O2 is consistent with a prior report on foetal HASM cells (Pandya et al. 2002). Thus, the HASM cells may be more tolerant to H2O2 than many other cell types including human fibroblasts (Miyoshi et al. 2006) and rat aortic vascular smooth muscle cells (Li et al. 2000), which undergo cell death at below 100 μM of H2O2. The ROS generated by 500 μM H2O2 greatly exceeds that generated by NPs at the doses used here (Xia et al. 2008; Frohlich et al. 2009). While it does not rule out a role for ROS generation, this observation suggests that the diverse particulate effects on viability and cell mechanics are unlikely to be mediated by generation of ROS.
In this study, we used the airway smooth muscle cell as a model to investigate the effects of eight particle species on cell viability and mechanics. The particles fell into four categories, based on their respective effect on viability and on mechanics (table 2). In support of the enhanced sensitivity of our biomechanics assay, we demonstrated that particles could dose dependently alter cell mechanics with little or no concomitant change in cell viability. In this section, we first discuss particle-size effects. This is followed by a discussion of the mechanism underlying the action of NPs, focusing on NP–macromolecule interaction. We close the discussion by envisioning further applications of biomechanics as a key cellular response and associated pathobiological implications of NP exposure.
A key characteristic of NPs is their significantly increased surface area relative to the same mass of MPs (Oberdorster et al. 2005; Nel et al. 2006). Particle surface area is proportional to the square of particle diameter, whereas the particle mass is proportional to the cube of particle diameter. It follows that for a given mass, particle surface area is inversely proportional to particle diameter. Enhanced particle surface area with reduced particle diameter can promote direct contact between the constituent atoms or molecules with the macromolecules of the cell; alternatively, that can accelerate dissolution of the particles.
For materials that are largely insoluble, comparisons between NPs and microparticles suggest that the biological responses can be unified if the particle dose was expressed in surface area per unit volume (Sager et al. 2008; Sager & Castranova 2009; Waters et al. 2009). For CuO particles, their toxicity may not be attributable to the Cu2+ ions because copper chelators desferoxamine and d-penicillamine did not reduce the particle toxicity (Fahmy & Cormier 2009). Thus, CuO toxicity is mainly through direct contact between the particle surface and the cell. Indeed, we observed greatly enhanced toxicity of the CuO NPs compared with that of the CuO MPs at a given mass dose, the former having approximately 100 times the surface area of the latter. Our observation of this enhanced toxicity for the CuO NPs is consistent with the findings of others (Fahmy & Cormier 2009; Karlsson et al. 2009).
While CuO is largely insoluble, ZnO is quite soluble (Xia et al. 2008). Previous studies on eukaryotes have found little difference between ZnO NPs of different sizes (Deng et al. 2009; Lin et al. 2009). Consistent with this, here we found only a moderate difference in cytotoxicity between ZnO NPs and ZnO MPs. This difference probably results from a difference in dissolution rate, with the NPs dissolving faster than the MPs. Nonetheless, for a difference of 1000-fold in particle size, the difference in LD50 was only 49 per cent. Thus, while the efficacy of insoluble particles is largely determined by their surface area, the efficacy of soluble particles is mainly determined by their mass.
The cytotoxic and physiological effects of NPs are currently unclear. Copper chelators did not inhibit the cytotoxicity of CuO NPs, suggesting that the toxicity is associated with the CuO particles (Fahmy & Cormier 2009). Those authors further demonstrated that CuO NPs generated a moderate amount of ROS, yet there was much oxidation of glutathione and production of 8-isoprostane, both pointing to increased oxidative stress; the cytotoxicity and production of 8-isoprostane could be partially inhibited by resveratrol, an antioxidant (Fahmy & Cormier 2009). We observed similar cytotoxicity of the CuO NPs on HASM cells. However, the cells were resistant to the application of high concentration of ROS (H2O2), suggesting a relatively high capacity of the native antioxidant machinery. We suggest that the induction of oxidative stress without much production of ROS by the CuO NPs (Fahmy & Cormier 2009) is more likely owing to a direct inhibition of the antioxidant macromolecules by the particles. Furthermore, certain NPs are cytotoxic in the absence of oxidative stress (Frohlich et al. 2009). We cannot rule out ROS generation and oxidative stress as consequences of cell–NP interaction, but they might be downstream of NP–macromolecule interaction, as we further argue below.
Data from others and the current study suggest that ZnO toxicity is mainly a consequence of soluble Zn2+. The specific mechanism of zinc toxicity is still unclear, but it is known that at least 10 per cent of the proteome has Zn2+ binding domains (Li & Maret 2009; Maret & Li 2009). The free intracellular Zn2+ is normally extremely low and tightly regulated. Thus, dissociated Zn2+ from ZnO particles can overwhelm the buffering capacity of key proteins such as the metallothioneins (Henkel & Krebs 2004; Li & Maret 2008). The excessive free Zn2+ can bind to and change conformations of a wide range of proteins, and this can lead to massive dysregulation of the signalling pathways, ultimately causing cell death. Thus, we suggest that probing both specific and non-specific interactions between NPs and macromolecules is vital to understanding the diverse biological effects of NPs (Klein 2007).
Diverse macromolecules in cells assemble into filaments and form the cytoskeleton. It is the cytoskeleton that confers stiffness and contractility to the cell (Elson 1988; Zhu et al. 2000; Lim et al. 2006b). Measuring these properties can therefore serve as a sensitive tool for probing the organization of the cytoskeleton (Lim et al. 2006a; Suresh 2007; Zhou et al. in press), and also the signalling pathways that control the cytoskeleton. NPs may alter cytoskeletal organization and processes through direct or indirect mechanisms. While most NPs enter the cell via caveolin- and clathrin-mediated endocytosis, a subset of NPs enter the cell by adhesive interactions and are found free in the cytoplasm (Geiser et al. 2005; Rothen-Rutishauser et al. 2009). This subset of NPs thus have the potential to directly interact with the cytoskeleton and the contractile machineries. Alternatively, particles can inhibit, cluster or even signal to cell-surface receptors, and thus result in downstream changes in cytoskeletal structure (as probed using cell stiffness) and altered receptor signal transduction (as probed using histamine/isoproterenol responses, both targeting cell-surface receptors). Indeed, our biomechanical assays revealed sensitive alterations in the stiffness and pharmacological responses when the HASM cells are exposed to a few specific particulates.
Our findings demonstrating alterations in cytoskeleton mechanics relate to a few prior reports and can shed light on the action of NPs. Inhalation exposure of rats to gold NPs resulted in significant downregulation of many muscle genes, such as myosin, troponin and tropomyosin, in the lung (Yu et al. 2007). Thus, the inhaled gold NPs may have induced changes in the pulmonary vessel smooth muscle and/or the respiratory smooth muscle. It remains to be investigated whether this downregulation in muscle genes was a direct consequence of particle exposure or downstream of inflammation. Nonetheless, our results on the airway smooth muscle cells suggest that direct particle exposure has the potential to effect such smooth muscle inhibition. In another study, nanosized, but not micrometre-sized, carbon black particles were able to inhibit the contraction of collagen matrix by lung fibroblasts; this implies that NPs can impair tissue repair (Kim et al. 2003). More importantly, this collagen-gel contraction study also supported the notion that the mechanical function of fibroblasts can be crucial, just as that of skeletal muscle cells, cardiac muscle cells and the airway smooth muscle cells studied here. In this regard, our findings established OMTC as a sensitive, high throughput tool for probing particulate effects on cellular mechanical function.
While previous in vivo and in vitro studies with inhaled particles had appropriately focused on the inflammatory response in the lung, direct interaction of NPs with key functional cells can potentially result in even more potent functional changes, such as the mechanical ones we demonstrated here. Our results highlight the susceptibility of cellular mechanical function to specific particulate exposure. Future application of cell mechanics to particulate research will help to identify pathogenic particle species or ingredients and contribute to a better understanding of the health effects of particulate exposure on humans.
We thank Douglas Dockery, Justin Mih, Yuan Li, and Dhananjay Tambe for discussions.
One contribution to a Theme Supplement ‘Mechanobiology’.