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In this study, primary rat alveolar epithelial cell monolayers (RAECM) were used to investigate transalveolar epithelial quantum dot trafficking rates and underlying transport mechanisms.
Trafficking rates of quantum dots (PEGylated CdSe/ZnS, core size 5.3 nm, hydrodynamic size 25 nm) in the apical-to-basolateral direction across RAECM were determined. Changes in bioelectric properties (ie, transmonolayer resistance and equivalent active ion transport rate) of RAECM in the presence or absence of quantum dots were measured. Involvement of endocytic pathways in quantum dot trafficking across RAECM was assessed using specific inhibitors (eg, methyl-β-cyclodextrin, chlorpromazine, and dynasore for caveolin-, clathrin-, and dynamin-mediated endocytosis, respectively). The effects of lowering tight junctional resistance on quantum dot trafficking were determined by depleting Ca2+ in apical and basolateral bathing fluids of RAECM using 2 mM EGTA. Effects of temperature on quantum dot trafficking were studied by lowering temperature from 37°C to 4°C.
Apical exposure of RAECM to quantum dots did not elicit changes in transmonolayer resistance or ion transport rate for up to 24 hours; quantum dot trafficking rates were not surface charge-dependent; methyl-β-cyclodextrin, chlorpromazine, and dynasore did not decrease quantum dot trafficking rates; lowering of temperature decreased transmonolayer resistance by approximately 90% with a concomitant increase in quantum dot trafficking by about 80%; and 24 hours of treatment of RAECM with EGTA decreased transmonolayer resistance by about 95%, with increased quantum dot trafficking of up to approximately 130%.
These data indicate that quantum dots do not injure RAECM and that quantum dot trafficking does not appear to take place via endocytic pathways involving caveolin, clathrin, or dynamin. We conclude that quantum dot translocation across RAECM takes place via both transcellular and paracellular pathways and, based on comparison with our prior studies, interactions of nanoparticles with RAECM are strongly dependent on nanoparticle composition and surface properties.
Nanoparticles (with at least one dimension ≤100 nm) offer novel opportunities for biomedical applications, yet their mechanisms of interaction with biological cells, tissues, and organs (including the lung) have not been well defined. Recent reports have highlighted the need for systematic investigation of unknown, but potentially harmful, effects of nanomaterials in order to permit safer design and application in biomedicine.1–4 Ultrafine ambient particles (diameter <100 nm) overlap in size with engineered nanomaterials. Systematic studies of toxicity/trafficking of defined/trackable engineered nanomaterials in the lung as a portal of entry to the systemic circulation and end organs would provide insight into the environmental health effects of air pollution and design of inhaled drug delivery systems.
Distal airspaces of the lung are lined with two types of alveolar epithelial cells, ie, type I (ATI) and type II (ATII) pneumocytes. ATI cells have thin cytoplasmic extensions (<1 μm) that cover 90% of the internal surface area of the normal human lung and play an important role in gas exchange and alveolar fluid balance.5 ATII cells are involved in synthesis, secretion, and recycling of surfactant components and can transdifferentiate into ATI cells.6–8 However, due to the complex anatomy of the lung, specific mechanistic information regarding nanoparticle interactions with the lung is difficult to obtain from in vivo models. As an alternative approach, primary cultured rat ATII cells are known to undergo morphologic7 and phenotypic9 transition into ATI cell-like monolayers that can serve as a suitable in vitro model of the alveolar epithelial barrier for mechanistic investigations of transport and cell biology. Such rat alveolar epithelial cell monolayers (RAECM) exhibit relatively high transmonolayer resistance of about 2.5 kκ · cm2 and well formed tight junctions, consistent with the expected properties of alveolar epithelium in vivo.
Semiconductor nanocrystals (eg, quantum dots) have improved optical properties compared with other fluorochromes and are used for biological imaging (both in vitro and in vivo)10,11 and therapeutic applications (eg, drug delivery vectors12,13 and photosensitizers for phototherapy14,15). However, the core material of quantum dots (eg, cadmium) is toxic to cells and organisms, raising concerns regarding their suitability as biomarkers/labels.16,17 In addition, water dispersability, biocompatibility, chemical stability, and robust optical properties are required for the biological applications of quantum dots.18 Chemical coatings and/or surface layering are essential for meeting these requirements. These surface layers can prevent chemical degradation and/or leaching of toxic core materials, improving quantum dot cytocompatibility, and reducing their nonspecific binding.19 Numerous modifications of quantum dot surface chemistry have been explored, including functionalizable inorganic shells, such as silica20,21 or organic layer attachment, eg, polyethylene glycol (PEG)22 or bovine serum albumin.23 A surface modification using PEG is known to reduce cytotoxicity, and the amphiphilic properties of PEG result in enhanced solubility. Moreover, PEG modifications, ie, PEGylations, are well known to be biocompatible and nonimmunogenic, affording a long blood circulation time after intravenous injection by reducing opsonization via proteins and impeding uptake by macrophages in the reticuloendothelial system.24–29
It is currently thought that both the size and surface properties of nanoparticles affect the cytotoxicity and intracellular fate(s) of nanoparticles.30–33 In this regard, we recently reported the trafficking properties of polystyrene nanoparticles with variable sizes and surface charges across RAECM.30,31 In brief, trafficking rates of polystyrene nanoparticles across RAECM are dependent on both surface charge density and size, in that we found an approximately 20–40 times greater flux for positively (versus negatively) charged polystyrene nanoparticles of similar size and that larger polystyrene nanoparticles (about 100 nm) cross RAECM about 3–4 times slower than smaller polystyrene nanoparticles (20 nm) of similar surface charge.31 Polystyrene nanoparticles appear to be translocated across RAECM via nonendocytic transcellular pathways, possibly involving diffusion across the lipid bilayer of cell plasma membranes.30
In this study, we used PEGylated quantum dots with three surface modifications (amine-, carboxylate-, and non-modified) with which to characterize nanoparticle uptake/trafficking into/across RAECM. We found that these quantum dots do not affect the barrier properties of alveolar epithelium. They translocate across RAECM via both transcellular pathways (which appear to be independent of caveolin-, clathrin-, or dynamin-mediated endocytosis) and paracellular routes.
The detailed procedure for preparation of RAECM has been described previously.34,35 This method involving the use of rats has been approved by the Institutional Animal Care and Use Committee of the University of Southern California. Briefly, ATII cells were freshly isolated from adult male, specific pathogen-free, Sprague-Dawley rats (125–150 g) using elastase digestion and enriched by IgG panning.34,35 Enriched ATII cells were plated onto tissue culture-treated polycarbonate filters (Transwell, 12 mm diameter, 0.4 μm diameter pores, Corning-Costar, Cambridge, MA) at 1.2 × 106 cells/cm2. ATII cells were cultured in MDS ( minimal defined serum-free medium with 10% newborn bovine serum from Omega, Tarzana, CA). Minimal defined serum-free medium consists of a 1:1 mixture of Dulbecco’s modified Eagle’s medium and Ham’s F-12 medium (Sigma, St Louis, MO) supplemented with 1 mM nonessential amino acids (Sigma), 100 U/mL primocin (InvivoGen, San Diego, CA), 10 mM N-(2-hydroxyethyl) piperazine-N′-(2-ethanesulfonic acid) (Sigma), 1.25 mg/mL bovine serum albumin (BD Bioscience, San Jose, CA), and 2 mM L-glutamine (Sigma). Cells were maintained at 37°C in a humidified atmosphere of 5% CO2 and 95% air and fed every other day starting on day 3 in culture when confluent monolayers were formed. Transmonolayer resistance and potential difference were screened using a Millicell-ERS device (Millipore, Bedford, MA). The equivalent active ion transport rate was calculated as potential difference/transmonolayer resistance. We utilized RAECM at 4–7 days in culture with transmonolayer resistance >2.5 kκ · cm2 and a potential difference >10 mV.
PEGylated quantum dots (CdSe/ZnS, core size 5.3 nm, hydrodynamic size 25 nm) which were non-modified, amine-modified, or carboxylate-modified, were purchased from eBioscience (San Diego, CA). Excitation/emission wavelengths were 360/610 nm for all quantum dots studied. Quantum dot zeta potential in water was determined using a Zetasizer (Malvern, Worcestershire, UK) with a measurement cell (with built-in electrodes) filled with 1 mL of various quantum dots suspended in water at 6.25 μg/mL by applying an electric field across the two electrodes.
To measure rates of quantum dot translocation across RAECM, apical fluid was replaced at t = 0 with fresh culture medium containing various quantum dots at 6.25 μg/mL. Apical-to-basolateral flux of quantum dots was estimated from quantum dots appearing in the basolateral fluid for up to 24 hours at 37°C. Quantum dot concentrations in downstream fluid were estimated spectrofluorometrically using SpectraMax M2 (Molecular Devices, Sunnyvale, CA). Apical [quantum dot] was determined at t = 0 and at the end of flux experiments. [Quantum dot] of various samples was calculated using a standard curve generated with known concentrations of quantum dots in MDS. Flux (J ) was calculated as J = (CV)/S/Δt, where C is [quantum dot] in basolateral fluid at time t = Δt, V is basolateral fluid volume (1.5 mL), S is nominal surface area of the monolayer (1.13 cm2) and Δt is length of time for flux measurement (6 or 24 hours).
In order to determine the effects of “leakier” tight junctions (increased tight junctional conductance) on trafficking rates of quantum dots across RAECM, quantum dot flux was measured in the presence of 2 mM ethylene glycol-bis(β-aminoethyl ether) N,N,N′,N′-tetra-acetate (EGTA, Sigma) in both apical and basolateral fluids. RAECM were pretreated with EGTA for 30 minutes, followed by apical instillation of carboxylate-, amine-, or non-modified quantum dots at a final concentration of 6.25 μg/mL with continued presence of 2 mM EGTA in both apical and basolateral fluids for 24 hours. Control monolayers were exposed apically to various quantum dots (6.25 μg/mL) in the absence of EGTA in the apical and basolateral fluids for 24 hours. Flux of quantum dots was assessed as described above. Bioelectric properties (ie, transmonolayer resistance, equivalent active ion transport rate, and potential difference) of RAECM in the presence and absence of EGTA were determined over time.
To determine the effects of energy depletion, the flux of amine-, carboxylate-, or non-modified quantum dots across RAECM was measured at 4°C (and 37°C) over 6 hours using an apical [quantum dot] of 6.25 μg/mL.
To explore if quantum dot translocation across RAECM involves endocytotic mechanisms, methyl-β-cyclodextrin, chlorpromazine, and dynasore were used to disrupt lipid raft-mediated endocytosis,30,32,36,37 clathrin-mediated endocytosis,30,38 and dynamin-dependent endocytosis (including clathrin-mediated and caveolin-mediated endocytosis),30,32,39 respectively. Briefly, RAECM were pre-treated for 30 minutes with methyl-β-cyclodextrin (200 μM, Sigma), chlorpromazine (28 μM, Sigma), or dynasore (80 μM, Sigma) in both apical and basolateral fluids. RAECM were then exposed apically to amine-, carboxylate-, or non-modified quantum dots (6.25 μg/mL), and the flux of these quantum dots was assessed as described above. Endocytosis inhibitors were present in both apical and basolateral fluids throughout the duration of the flux experiments. Control monolayers were exposed apically to amine-, carboxylate-, or non-modified quantum dots (6.25 μg/mL) without these inhibitors. To determine if dynasore inhibits dynamin-dependent endocytosis, flux of fluorescein isothiocyanate-cholera toxin subunit B (50 μg/mL, Sigma), which involves caveolae-mediated endocytosis,30 or Alexa 594-transferrin (500 μg/mL, Invitrogen), which involves clathrin-mediated endocytosis,30 was measured in the presence and absence of dynasore. Bioelectric properties (ie, transmonolayer resistance, equivalent active ion transport rate, and potential difference) of RAECM in the presence and absence of inhibitors were determined over time.
RAECM were exposed apically to 6.25 μg/mL amine-, carboxylate-, or non-modified quantum dots at 37°C for 24 hours. RAECM were then washed three times with ice- cold, phosphate-buffered saline (pH 7.2) and fixed with ethanol at −20°C for 5 minutes. Fixed RAECM were incubated with phosphate-buffered saline containing both 5% bovine serum albumin and 0.2% TX-100 for 1 hour at room temperature. Rabbit antibody against zonula occludens-1 (Zymed Laboratories, San Francisco, CA), diluted (1:100) in phosphate-buffered saline containing 1% bovine serum albumin was then incubated with RAECM for 1 hour at 37°C. Goat antirabbit antibody conjugated with Alexa 488 (Invitrogen) was diluted to 1:100 using 1% bovine serum albumin in phosphate-buffered saline and used to incubate RAECM at 37°C for 1 hour. These RAECM were rinsed with phosphate-buffered saline and mounted on microscope slides with mounting medium containing the nuclear staining dye 4′,6-diamidino-2-phenylindole (DAPI) (Vector, Burlingame, CA). RAECM not exposed to quantum dots or those incubated with primary or secondary antibody alone served as negative controls and were similarly processed. Images were acquired with a Leica TCS SP5 confocal fluorescence imaging system (Leica Microsystems, Heidelberg, Germany). The SP5 system was built around a Leica DM6000 CS inverted microscope which is powered by a wideband, fully automated, infrared (680–1080 nm) combined photo-diode pump laser and mode-locked titanium:sapphire laser ( Cameleon Ultra II, Coherent, Santa Clara, CA) for multiphoton excitation, and/or by HeNe and Ar lasers for conventional one photon-excitation confocal microscopy. Alexa 488 and DAPI were excited at 488 and 740 nm, with emission observed at 500–535 nm and 400–460 nm, respectively.
Data are presented as the mean ± standard error of the mean (n = total number of RAECM utilized). Student’s t-tests were performed for comparisons of two group means. One-way analysis of variance followed by post hoc tests based on modified Newman–Keuls procedures was performed to determine statistical significance among means of at least three groups. P < 0.05 was considered to be statistically significant. Statistical analyses were carried out using Sigmaplot software (San Jose, CA).
A summary of zeta potentials of quantum dots utilized in this study measured in water is shown in Table 1. Although the PEG surface of quantum dots are amine-, carboxylate-, or non-modified, all quantum dots exhibited negative zeta potentials, ranging from −15 mV for amine-modified quantum dots to −31 mV for non-modified quantum dots.
Figure 1 shows trafficking rates of amine-, carboxylate-, and non-modified quantum dots across RAECM when assessed after 24 hours of exposure at an apical [quantum dot] of 6.25 μg/mL. Trafficking rates of these quantum dots do not appear to be affected by surface charge density within the range studied herein. Bioelectric properties (ie, transmonolayer resistance, equivalent active ion transport rate, and potential difference) of RAECM did not change significantly in the apical presence of 6.25 μg/mL quantum dots for 24 hours (data not shown).
Flux of amine-, carboxylate-, and non-modified quantum dots in the absence of EGTA was 0.013 ± 0.002, 0.017 ± 0.002, and 0.016 ± 0.004 pg/cm2/second, respectively, and increased by about 50%–130% in the presence of 2 mM EGTA (Figure 2). Concomitantly, transmonolayer resistance decreased by about 95% in the presence of 2 mM EGTA (data not shown). After replacing the bathing media with fresh MDS (without EGTA), transmonolayer resistance recovered by 75% over 12 hours (data not shown).
Flux of amine-, carboxylate-, and non-modified quantum dots at 37°C was 0.085 ± 0.007, 0.103 ± 0.015, and 0.111 ± 0.012 pg/cm2/second, respectively, and all increased by approximately 85% after 6 hours at 4°C (Figure 3). Transmonolayer resistance after 6 hours at 4°C was about 5% of the respective control (data not shown). Transmonolayer resistance recovered to approximately 75% of that before reducing temperature to 4°C when temperature was increased to 37°C (data not shown).
Figure 4 shows flux of amine-, carboxylate-, and non-modified quantum dots in the presence or absence of 200 μM methyl-β-cyclodextrin. Flux of amine-, carboxylate-, or non-modified quantum dots in the absence of methyl-β-cyclodextrin was 0.013 ± 0.003, 0.016 ± 0.002, and 0.012 ± 0.003 pg/cm2/second, respectively, and did not decrease in the presence of methyl-β-cyclodextrin compared with the respective control. Previously, we showed that flux of cholera toxin subunit B (apical concentration 50 μg/mL, used as a positive control) across RAECM decreased by about 75% in the presence of 200 μM methyl-β-cyclodextrin.30 Transmonolayer resistance of RAECM treated with methyl-β-cyclodextrin did not change compared with that of the control (data not shown).
Flux of amine-, carboxylate-, and non-modified quantum dots at baseline was 0.016 ± 0.002, 0.017 ± 0.001, and 0.018 ± 0.001 pg/cm2/second, respectively, and did not decrease in the presence of 28 μM chlorpromazine compared with the respective control (Figure 5). Previously, we showed that flux of transferrin (apical concentration 500 μg/mL, used as a positive control) decreased by about 85% in the presence of chlorpromazine.30 Transmonolayer resistance of RAECM treated with chlorpromazine did not change compared with that of the control (data not shown).
Figure 6 shows flux of amine-, carboxylate-, and non-modified quantum dots in the presence or absence of 80 μM dynasore. Flux of amine-, carboxylate-, and non-modified quantum dots in the absence of dynasore was 0.015 ± 0.002, 0.022 ± 0.002, and 0.027 ± 0.003 pg/cm2/second, respectively, and did not decrease in the presence of dynasore compared with the respective control. Flux of cholera toxin subunit B and transferrin (apical concentrations 50 μg/mL and 500 μg/mL, respectively, used as positive controls) in the absence of dynasore was 3.22 ± 0.12 and 29.54 ± 7.32 pg/cm2/second, respectively, and decreased by about 85% and 72%, respectively, in the presence of dynasore after 24 hours (data not shown). Transmonolayer resistance of RAECM treated with dynasore increased by approximately 30% (data not shown).
Confocal photomicrographs (Z-max) of RAECM after apical exposure to 6.25 μg/mL amine-modified quantum dots for 24 hours are shown in Figure 7. Quantum dots are seen predominantly in the cytosol, with no apparent localization at cell–cell borders (ie, paracellular pathways). Similar observations were noted with carboxylate- and non-modified quantum dots (data not shown).
This study demonstrates that apical exposure of RAECM to PEGylated quantum dots with amine-, carboxylate-, or non-modified surfaces for 24 hours does not affect alveolar epithelial barrier properties. Quantum dot translocation across RAECM via transcellular pathways does not appear to require caveolin-, clathrin-, or dynamin-dependent pathways, although quantum dot traffic via paracellular pathways may account (at least in part) for the observed fluxes.
We have previously reported that cationic polystyrene nanoparticles (amidine-modified, zeta potential about 71 mV) translocate across RAECM 20–40 times faster than anionic polystyrene nanoparticles (carboxylate-modified, zeta potential of about −45 mV).30,31 Although the range of surface charge of the amine-, carboxylate-, and non-modified PEGylated quantum dots was much less, no effect of surface charge on quantum dot flux across RAECM was seen.
No detectable translocation of quantum dots with non-modified, amine-modified, or carboxylate-modified surfaces ([apical quantum dot] = 25 nM) across RAECM over 24 hours was reported by Geys et al,40 while significant increases in transmonolayer resistance were observed. The quantum dots used by Geys et al40 were not PEGylated, although their hydrodynamic size and surface charge were similar to our quantum dots. The major difference between the studies is that measurable fluxes were noted for PEGylated quantum dots (our study) versus none for non-PEGylated quantum dots,40 likely due to differences in interactions between RAECM and differently coated quantum dots. Greater internalization of carboxylate-coated quantum dots compared with that of PEG-coated or PEG-amine-coated quantum dots has been reported for human epidermal keratinocytes.41
Although treatment of epithelial cells with EGTA (a calcium chelator) increases paracellular permeability to small solutes,42–45 it is unknown if nanoparticles traverse normal and/or EGTA-disrupted tight junctions. In this study, trafficking rates across RAECM of all three quantum dots with different surface modifications increased in the presence of 2 mM EGTA, indicating that these quantum dots traverse RAECM via tight junctional pathways following EGTA treatment. In contrast, Yacobi et al30 concluded that translocation of amidinated (20 and 120 nm) or carboxylated (20 and 100 nm) polystyrene nanoparticles across RAECM does not take place via paracellular pathways. Trafficking of small hydrophilic solutes (up to 10 nm) across epithelial barriers can occur via paracellular pathways,46,47 consistent with the small core size of the quantum dots utilized in this study (about 5 nm).
Quantum dot trafficking increased across RAECM when temperature was lowered from 37°C to 4°C. At lower temperature, energy-dependent mechanism(s) that may be involved in translocation of quantum dots transcellularly across RAECM will decrease or stop. However, when temperature was decreased to 4°C, transmonolayer resistance of RAECM decreased by about 90%, suggesting that trafficking of quantum dots is taking place primarily via paracellular pathways at low temperature.
Glycolipid rafts are detergent-insoluble, low-density membrane fractions that are rich in cholesterol and sphingolipids. 48 Methyl-β-cyclodextrin extracts cholesterol from plasma membranes and thereby inhibits lipid raft-mediated endocytosis (including caveolin-mediated endocytosis, CLIC/GEEC endocytosis, arf 6-mediated endocytosis, flotillin-mediated endocytosis, and macropinocytosis).37,38 We previously reported that 200 μM methyl-β-cyclodextrin markedly decreases flux of cholera toxin subunit B, a positive control for lipid raft-mediated transcytosis across RAECM.30 In the present study, flux of quantum dots observed in the presence of 200 μM methyl-β-cyclodextrin did not decrease, suggesting that translocation of quantum dots across RAECM is not taking place via lipid raft-mediated endocytosis. We have reported that translocation of polystyrene nanoparticles across RAECM and Madin Darby canine kidney type II cell monolayers (MDCK-II) was not decreased in the presence of 10–200 μM methyl-β-cyclodextrin.30,32
Clathrin is composed of three light and three heavy chains that form a triskelion. Assembly of the triskelion leads to formation of a net-like basket (clathrin-coated pit) at the cell plasma membrane. Involvement of clathrin-mediated endocytosis in uptake/translocation of various nanoparticles in cells and tissues, eg, amidine-modified polystyrene nanoparticles in MDCK-II,32 PEGylated D,L-polylactide (PLA) (PEG-PLA) nanoparticles into HeLa cells49 and fullerenic nanoparticles into rat fibroblasts and rat hepatoma cells,50 has been reported. Chlorpromazine and other inhibitors of clathrin- mediated endocytosis cause clathrin and AP-2 adaptor protein to relocate to multivesicular bodies and as a result inhibit clathrin-mediated endocytosis.51 We reported previously that transferrin utilizes clathrin-mediated endocytosis across RAECM which was inhibited by 28 μm chlorpromazine. 30 However, treatment of RAECM with 28 μM chlorpromazine in our current study did not decrease trafficking rates of any quantum dots utilized herein. It has been reported that a charge-dependent clathrin-mediated mechanism appears to be responsible for uptake of positively (but not negatively) charged PEG-PLA nanoparticles into HeLa and MDCK-II cells.49,52 In this regard, we recently reported that trafficking of positively (but not negatively) charged polystyrene nanoparticles across MDCK-II is clathrin-mediated.32
Dynamin, the membrane scission protein, is a large GTPase which forms a helical polymer around the neck of newly-formed cell plasma membrane invaginations and, upon GTP hydrolysis, mediates the fission of the vesicle from the plasma membrane. Dynamin is essential for caveolin-coated and clathrin-coated vesicle formation and appears to play a role in lipid raft-mediated processes as well. Dynasore, a small, cell-permeable molecule, reversibly inhibits the GTPase activity of dynamin-1 or dynamin-2 at the cell plasma membrane and rapidly blocks vehicle formation.53 Our data showing that trafficking rates of quantum dots did not decrease in the presence of 80 μM dynasore across RAECM are consistent with the lack of effect of inhibition of endocytosis involving clathrin or lipid rafts (including caveolin). Increased trafficking of quantum dots could be due to upregulation of other translocation pathways (although unlikely to include paracellular pathways with increased transmonolayer resistance) in the presence of dynasore. We reported recently that dynasore has no effect on trafficking rates of polystyrene nanoparticles (20 or 100/120 nm; amidine- modified or carboxylate-modified) across RAECM.30 On the other hand, 80 μM dynasore inhibited uptake of positively charged 100 nm polystyrene nanoparticles in HeLa cells by two-fold compared with that of negatively charged polystyrene nanoparticles of comparable size.54
Phagocytosis is prevalent in macrophages and dendritic cells, although it can be induced in most cells by expression of requisite receptors.55 Phagocytosis has also been reported for ATI and ATII cells.56 Internalization of large particles and microorganisms, typically greater than 0.5 μm, is known to occur via phagocytosis,37 but it is unlikely that PEGylated quantum dots (core size 5.3 nm, hydrodynamic size 25 nm) are significantly phagocytosed.
In summary, we have shown that translocation of amine-, carboxylate-, and non-modified PEGylated quantum dots across RAECM occurs both transcellularly (not involving major endocytic pathways) and paracellularly. Compared with trafficking of polystyrene nanoparticles across RAECM and MDCK-II, nanoparticle interactions with epithelial barriers appear to be both cell type-specific and dependent on nanoparticle physicochemical properties (eg, size, surface charge, and composition).
This work was supported in part by the Hastings Foundation, Whittier Foundation, and research grants (EY011386, EY017293, EY016985, ES017034, ES018782, HL038578, HL038621, HL062569, and HL089445) from the National Institutes of Health. Dr Crandall is Hastings Professor and Norris Chair of Medicine. Dr Borok is Edgington Chair in Medicine.
The authors report no conflicts of interest in this work.