Dilemmas in the reliable estimation of the in-vitro cell viability in magnetic nanoparticle engineering: which tests and what protocols?
© Hoskins et al; licensee Springer. 2012
Received: 14 September 2011
Accepted: 16 January 2012
Published: 16 January 2012
Magnetic nanoparticles [MNPs] made from iron oxides have many applications in biomedicine. Full understanding of the interactions between MNPs and mammalian cells is a critical issue for their applications. In this study, MNPs were coated with poly(ethylenimine) [MNP-PEI] and poly(ethylene glycol) [MNP-PEI-PEG] to provide a subtle difference in their surface charge and their cytotoxicity which were analysed by three standard cell viability assays: 3-(4,5-dimethylthiazol-2-yl)-5-(3-carboxymethoxyphenyl)-2-(4-sulfophenyl)-2H-tetrazolium [MTS], CellTiter-Blue and CellTiter-Glo (Promega, Southampton, UK) in SH-SY5Y and RAW 264.7 cells The data were validated by traditional trypan blue exclusion. In comparison to trypan blue manual counting, the MTS and Titer-Blue assays appeared to have consistently overestimated the viability. The Titer-Glo also experienced a small overestimation. We hypothesise that interactions were occurring between the assay systems and the nanoparticles, resulting in incorrect cell viability evaluation. To further understand the cytotoxic effect of the nanoparticles on these cells, reactive oxygen species production, lipid peroxidation and cell membrane integrity were investigated. After pegylation, the MNP-PEI-PEG possessed a lower positive surface charge and exhibited much improved biocompatibility compared to MNP-PEI, as demonstrated not only by a higher cell viability, but also by a markedly reduced oxidative stress and cell membrane damage. These findings highlight the importance of assay selection and of dissection of different cellular responses in in-vitro characterisation of nanostructures.
Keywordsmagnetic nanoparticle cellular interaction cytotoxicity cell viability assay zeta potential.
Magnetic nanoparticles [MNPs] have assumed importance for the imaging of diseases such as cancer and diabetes . In the field of tissue engineering, magnetic nanoparticles have been previously reported for many applications including cellular labelling, sorting and monitoring, targeted in-vivo therapeutic delivery, stem cell replacement therapy and welding tissue surfaces [2, 3]. In 2007, Syková and Jenelová incorporated superparamagnetic nanoparticles into mesenchymal stem cells for the regeneration of tissue damage in the central nervous system . They reported that the superparamagnetic nanoparticles enabled imaging and control of cellular migration by external magnetic fields to the wound site, optimised the number of cells needed and also helped monitor any possible side effects . Some superparamagnetic nanoparticles were previously approved for imaging and therapeutic applications in humans, e.g. Feridex IV® and Combidex® (Advanced Magnetics Inc., Lexington, MA, USA) [5–7] and several other superparamagnetic nanoparticles are also undergoing phases I and II clinical trials [1, 5, 8, 9].
Despite increased applications of MNPs emerging, little is known of the adverse biological side effects due to their nanoscale size. Recently, the importance of such biological characterisation and cytotoxic profile has been recognised. The use of appropriate assessments is vital in evaluating the biocompatibility of MNPs. At present, a range of assays are used which measure cell viability through non-specific enzyme activity (3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide [MTT], 3-(4,5-dimethylthiazol-2-yl)-5-(3-carboxymethoxyphenyl)-2-(4-sulfophenyl)-2H-tetrazolium [MTS], CellTiter-Blue assay) or via ATP level (CellTiter-Glo assay). However, little has been documented about the possible interactions between nanoparticles and the reagents used in these assays. The validation of these assays therefore merits urgent investigation.
Recently, Häfeli et al. reported a modification in their MTT assay used to measure the cytotoxicity of polyethylenoxide-coated magnetic nanoparticles . Fisichella et al. reported that mesoporous silica nanoparticles interfered with the intracellular trafficking of the MTT formazan vesicles in HeLa cells and astrocytes, resulting in an overestimation of cytotoxicity when compared to flow cytometry . In contrast, vast literature has been published on the effect of carbon nanotubes [CNTs] on such assays [12–18]. It has been documented that single-walled carbon nanotubes interfere with both absorbance and fluorescent cytotoxicity assays [12–14]. Belyanskaya et al. reported that the extent of interference can be attributed to three factors: (1) protocol of the assay, (2) surfactant coating and (3) chemical architecture of the CNT . Belyanskaya reported that addition of one further centrifugation step at the end of the MTT assay in order to lyse the cells and discard the cellular components and CNT particles could reduce interferences caused by the CNTs. They concluded that extreme caution should be used when interpreting cell viability data without appropriate controls in place .
Here, we determine the suitability of various standard cell viability assays for a MNP with a particle size of 100 nm. As MNP surface properties especially surface charge is an important factor in determining their biocompatibility [19, 20], the surface of commercial MNPs was modified with poly(ethylenimine) [MNP-PEI] and further conjugated with poly(ethylene glycol) [MNP-PEI-PEG]. PEI polymers have been reported to increase solution properties of nanoparticles and provide a platform for further modification, such as targeting or solubilisation moieties [21–23]. PEG has been widely accepted for nanostructure modification and drug delivery due to its biocompatibility and stealth properties in vivo [24–27]. Through surface modification, we obtained two types of MNPs with controlled difference on their surface charges, MNP-PEI having a higher positive charge than MNP-PEI-PEG, and used them as models to analyse the ability of various assays in discriminating the subtle difference in the level of effect those nanoparticles could impose to cells. Another consideration in assessing the sensitivity of the cell viability assays is MNP concentration. Concentrations of MNPs closer to physiological conditions and much lower than that reported in most studies were used in the present study. We validated the cell viability data obtained from commonly used MTS, CellTiter-Blue and CellTiter-Glo assays by comparing them with that obtained with traditional trypan blue exclusion to evaluate the suitability of those commercial cell viability assays for nanotoxicity studies. The validated data were further complemented by measurement of a number of cellular events in response to MNPs including cell membrane integrity, reactive oxygen species [ROS] production and lipid peroxidation [LPO] to give a more comprehensive safety profile.
Coating and characterisation of magnetic nanoparticles
MNPs (Chemicell GmbH, Berlin, Germany) diluted with 9.5 mL deionised water [DI] were sonicated for 18 h. N-(3-dimethylaminopropyl)-N-ethylcarboimide hydrochloride (5.7 mg) and N-hydroxysuccinimide (11.4 mg) dissolved in 1.9 mL of 2-(N-Morpholino)ethanesulfonic acid hemisodium salt [MES] buffer (0.5 M) were added to the solution and stirred for 1 h at room temperature [RT]. MES buffer (0.1 M) was added, and the solution was centrifuged at 40,000 × g at 4°C for 0.5 h. MNPs were resuspended in the MES buffer (0.1 M, 19 mL) containing 0.95 mg PEI (molecular weight [MW] 750,000) and stirred at RT for 3 h. Glycine (25 mM) in phosphate-buffered saline [PBS] (9.5 mL) was added, and the solution was stirred for a further 1 h at RT. The nanoparticles were 'washed' with DI (three times), and the resultant MNP-PEI eluted from the solution using a high-powered magnet. The nanoparticle pellet was resuspended in 10 mL of DI.
MNP-PEI (4 mL) was added to 0.08 M sodium tetraborate (12 mL) followed by methoxypolyethylene glycol p-nitrophenyl carbonate (MW 5,000) (20 mg) with stirring for 3 h at RT in the absence of light. The resultant solution was washed with DI, and the MNP-PLL-PEGs eluted from the solution using a high-powered magnet. The nanoparticles were resuspended in 4 mL DI.
Nanoparticle concentration was determined using inductively coupled plasma [ICP] analysis and dispersed in DI before sonication for 10 min before subsequent measurements. Hydrodynamic diameters, polydispersity index and zeta potential measurements were carried out using a photon correlation spectrometer (Zetasizer Nano-ZS, Malvern Instruments, Worcestershire, UK). All measurements were conducted in triplicate at 25°C, and an average value was determined. Prior to zeta potential analysis, standard control samples were run on the instrument.
Culture of cell lines
Two cell lines, SH-SY5Y (human neuroblastoma; ATCC, Manassas, VA, USA) and RAW 264.7 (mouse macrophage), were used in our study. Neuroblastoma cells are being used to represent cells present at the regenerative site during nerve regeneration, and macrophage cells are the body's first line of defence for the immune system, phagocytosing foreign bodies and cleaning the blood of unknown particles; hence, any particles administered to the site of nerve injury will encounter these cells. SH-SY5Y cells were cultured in 50:50 Dulbecco's minimum essential medium [DMEM]: Ham's F-12 media containing 10% heat inactivated foetal bovine serum [FBS], 2 mM L-glutamine and 1% penicillin streptomycin [Penstrep] (all purchased from Invitrogen Ltd., Renfrew, UK). RAW264.7 cells (kindly donated by Prof. Colin Watts and Dr Alan Prescott, College of Life Sciences, University of Dundee, Dundee, UK) were cultured in DMEM containing 10% FBS, 2 mM L-glutamine and 1% Penstrep. Cells were grown under standard conditions (37°C and 5% CO2) to reach a confluency of 70% to 80% before being subjected to any further experimentation.
Cellular uptake of nanoparticles measured by inductively coupled plasma
Cells seeded in 6-well plates and incubated with MNPs at final concentrations of 0, 1.56, 6.25 and 25 μg mL-1 (the concentration of MNPs used for all experiments indicates the concentration of Fe3+) for 24 h. The medium was removed, and the cells were thoroughly washed with PBS for three times, trypsinised and resuspended in medium. The cell number was counted using a haemocytometer, and cells were placed in eppendorf tubes (1 × 106 cells/tube). The cell suspensions were centrifuged at 800 rpm for 5 min, and the supernatant was discarded. Concentrated hydrochloric acid (100 μL) was added to the cells, and the tubes were incubated at 90°C for 0.5 h. The samples were cooled to room temperature and centrifuged at 1,500 rpm for 10 min. The supernatant was diluted with deionised water and run on an ICP instrument (Optima 7000V DV, PerkinElmer, Wokingham, UK). A calibration was carried out using iron standard solutions of 0.5 to 5 μg mL-1 (R = 0.9999). A control sample of deionised water was also run.
Observation of cellular uptake of nanoparticles by transmission electron microscopy
MNPs were added to cells cultured in 75-cm2 flasks (6.25 μg mL-1) for 24 h. The cells were washed with PBS (three times). A 10-mL fixative (4% paraformaldehdye, 2.5% gluteraldehyde in PIPES buffer, pH 7.2) was added to the flasks and incubated for 0.5 h at room temperature. The cells were scraped off the flask and centrifuged into a pellet. The pellet was set in resin, and micron-sized slices were cut. The specimens were viewed using transmission electron microscopy [TEM] (JEM.1200ex, JEOL Ltd., Herts, England, UK), and images were recorded in digital imaging plates and scanned in a Ditabis Micron scanner (Ditabis AG, Pforzheim, Germany).
Cell viability determination by MTS, CellTiter-Blue and CellTiter-Glo assays
MTS and CellTiter-Blue are colorimetric and fluorescent assays (respectively) used to measure cell viability via non-specific redox enzyme activity. CellTiter-Glo is a luminescent assay used to measure cell viability by ATP level. Cells (100 μL, 1 × 105 cells/ml) were seeded into a 96-well flat-bottomed plate (white for Titer-Glo) and incubated for 24 h at 37°C with 5% CO2. The medium was replaced with increasing MNP concentrations (1.56 to 25 μg mL-1) (in triplicates). The cells were incubated for 24, 72, 120 and 168 h (for 120- and 168-hr incubations, the medium was replaced at 72 h with fresh medium containing appropriate concentrations of MNPs). The cells were washed (with PBS, three times) and replaced with fresh medium (100 μL). MTS (20 μL) or CellTiter-Blue (20 μL) reagents were added to the wells, and the plate was incubated for 4 h protected from light. Absorbance (MTS) was recorded at 490 nm, and fluorescence intensity (CellTiter-Blue) was recorded (excitation 560 nm, emission 590 nm). To eliminate possible interference between MNPs and assay readings, cells treated with same concentrations of MNPs but without addition of assay reagents were used as blank wells. Both assays were measured on a Tecan M200 multimode plate reader (Tecan Austria GmbH, Grödig, Austria). CellTiter-Glo reagent was added to the wells (50 μL and 50-μL media) and incubated at room temperature for 10 min protected from light. The luminescence was recorded using the same multimode plate reader. As per MTS and Titer-Blue assays, blank wells (with no reagents) were measured for luminescence and deducted from the values in experimental wells. Values of viability of treated cells were expressed as a percentage of that from corresponding control cells. All experiments were repeated at least three times. All assay kits were purchased from Promega, Southampton, UK.
Trypan blue exclusion assay
Cells were seeded into a 12-well plate and incubated for 24 h at 37°C with 5% CO2. The cells were treated as previously described in MTS, Titer-Blue and Titer-Glo. The cells were washed with PBS three times and trypsinised. Trypan blue was added to a 100-μL cell suspension in an equal volume and incubated at room temperature for 5 min. The viable cells were counted using a Countess™ automated cell counter (Invitrogen, Ltd., Renfrew, UK). Values of viability of treated cells were expressed as a percentage of that from corresponding control cells. All experiments were repeated at least three times.
Reactive oxygen species assay
Cells were seeded into a 96-well plate (10,000/well) and incubated for 24 h. Cells were incubated with increasing MNP concentrations (1.56 to 25 μg mL-1) for 1, 4, 24 and 72 h. The cells were washed three times with PBS and incubated for 1 h with 100-μM carboxy-H2DCFDA (Invitrogen Ltd., Renfrew, UK) in PBS at 37°C protected from light. The cells were washed three times with PBS and incubated with a 100-μL serum-free medium for a further 0.5 h. The medium was replaced with PBS. The fluorescence intensity of the samples was measured at 560 nm (excitation) and 590 nm (emission) on a Tecan M200 microplate reader (Tecan Austria). The percentage of dichlorofluorescin [DCF] fluorescence was calculated in respect to control cells assumed to be 100%.a
Lipid peroxidation measurement by thiobarbituric acid reactive substance assay
Cells in an exponential growth phase were seeded into a 6-well plate and incubated for 24 h. The medium was replaced with increasing MNP concentrations (1.56 to 25 μg mL-1). After incubation, the medium was removed, and the wells were washed three times with PBS. Cells were trypsinised and resuspended in 0.5 mL PBS containing 0.05% butylated hydroxytoluene on ice. The cell suspensions were sonicated for 5 s three times at 40 V and were kept on ice. Malondialdehyde bis(dimethyl acetal) [MDA] standard solutions (0 to 5 μM) were prepared, and 100 μL of samples or standards was added to the Eppendorf tubes. Sodium dodecyl sulphate (100 μL, 2%) was added, and the tubes were incubated for 5 min at room temperature. Thiobarbituric acid (250 μL) was added to the eppendorf tubes before incubation at 95°C for 1 h. The samples were cooled on ice for 10 min and centrifuged at 3,000 rpm for 15 min at 4°C. The supernatant was pipetted into the wells of a 96-well plate, and fluorescent measurements were taken at 530 nm (excitation) and 550 nm (emission). The results were calculated as nanomoles of MDA per milligram of cellular protein. Protein content was determined by the addition of a 100-μL sample to a 3-mL Bradford reagent. The samples were mixed well at room temperature for 5 min, and absorbance was measured at 595 nm. The absorbance values were compared to a calibration curve carried out using bovine serum albumin, and the protein concentration was determined.a
Cell membrane integrity analysis
Cells were seeded into a 96-well plate (15,000/well) and grown for 24 h. The medium was replaced with increasing magnetic nanoparticle concentrations (1.56 to 25 μg mL-1). The plates were incubated for 1, 4, 24 and 48 h. After incubation 2 μL of lysis buffer was added to the positive control wells, and the plate was centrifuged at 1,500 rpm for 10 min at 37°C. After centrifugation, 50 μL of the supernatant was removed from each well and placed into a new plate, and 50 μL of a membrane integrity assay reagent was added to the wells. The plates were incubated for 10 min at 37°C protected from light. Twenty-five microlitres of stop reagent was then added to the wells, and the fluorescence of the samples was measured at 560 nm (excitation) and 590 nm (emission) on the microplate reader. The percentage of cytotoxicity with respect to the positive control wells was calculated, whereby the lysed cells were assumed to have 100% lactate dehyrogenase [LDH] release.a
Coating and characterization of magnetic nanoparticles
The particles were successfully coated with PEI and further functionalised with PEG. ICP was used to deduce the concentration of the MNPs after each reaction (based on the total iron content). The concentration after the initial coating with PEI was 1.39 mg mL-1 (74% yield) and 1 mg mL-1 (72% yield) after pegylation based on ICP analysis. After coating, the particles were noticeably more stable in the solution, especially after pegylation. The size of the MNPs was determined using photon correlation spectroscopy which measures the hydrodynamic radius of the particles in the solution [see Table S1 in Additional file 1]. The particles were measured at 0.25 mg mL-1 in deionised water. With polymer coating, the size of the commercial Chemicell nanoparticles increased from 101 nm to 146 nm (MNP-PEI); the size further increased upon pegylation to 361 nm.
The zeta potential of the 'naked' MNPs was negative (-38.2 mV), due to the -COOH groups on the surface of the particles [see Table S1 in Additional file 1]. Addition of a cationic polymer such as PEI increases the overall zeta potential, resulting in a positive value. This assumption can be made due to the positive charge on the amine groups of the polymer backbone, binding to the -COOHs thus rendering them neutral, plus and unbound amine groups which will still hold their positive charge. The PEI coating gave a positive value (+17.7 mV) which indicated that the polymer had been successfully coated with the polymer, which is in agreement with the size data [see Table S1 in Additional file 1]. The zeta potential measurement for the pegylated particle was +12.1 mV. This value indicated that pegylation had occurred as the zeta potential increased in negativity compared to that of the MNP-PEI due to the presence of -OH groups on the particle surface which is due to the PEG coating (MNP-PEI-PEG) [see Table S1 in Additional file 1].
Cellular uptake of nanoparticles
Table S2 in Additional file 1 shows the intracellular content of MNPs in SH-SY5Y and RAW 264.7 cells after 24 h incubation at different concentrations. In the SH-SY5Y cells, the cellular uptake was increased ninefold from 2.867 pg to 26.763 pg per cell (at 25 μg mL-1) upon PEI coating of the nanoparticles. After pegylation, an eightfold increase in cellular uptake was observed when compared to the uncoated MNPs at the same concentration. The increase in cellular uptake, which is dependent on surface properties of MNPs, further confirms the coating of the particles. Only a small increase in nanoparticle uptake was observed in RAW 264.7 upon coating (maximum of 1.6-fold and 1.7-fold increase by PEI and PEG, respectively) [see Table S2 in Additional file 1], thus indicating that the cellular uptake in RAW 264.7 cells is less affected by the surface properties of the nanoparticles compared to that in SH-SY5Y cells. This is consistent with the phagocytic nature of the RAW 264.7 cells. Compared to the SH-SY5Y cells, the RAW 264.7 cells achieved a lower cellular uptake; we postulate that the smaller cellular volume of the RAW 264.7 cells was a limiting factor compared with the much larger volume of SH-SY5Y cells.
Cell viability measured by MTS, CellTiter-Blue and CellTiter-Glo assays
In CellTiter-Blue assay, viable cells reduce resazurin into fluorescent resorufin. Similar to the MTS assay, the polymer-coated MNPs caused a significant increase in the fluorescent measurement (p < 0.05 with exception to 1.56 μg mL-1 MNP-PEI-PEG on SH-SY5Y cells), giving an overexpression with a similar trend in time dependency (Figure 2). This indicated that the presence of the nanoparticle in cellular environments increased the fluorescent intensity exhibited by the resorufin dye.
The results for the CellTiter-Glo assay (Figure 2) showed a similar trend to the MTS and CellTiter-Blue assays. Overall, with increased time and concentration, no significant difference from the actual cell viability was observed (based on trypan blue exclusion, see below) (p > 0.05). This was observed for both cell lines.
This unique phenomenon could be due to a number of factors, either the presence of the MNPs both intracellular and on the membrane of the cells or the nanoparticles themselves interfere with the reagents. In our experiments, wells with nanoparticles (intracellular or on the cell membrane) and without assay reagents were used as blanks and were deducted from experimental wells. Furthermore, nanoparticles with assay reagents in the absence of cells were also analysed, and no significant effect on absorbance, fluorescence or luminescent readout was observed (data not shown). Therefore, we hypothesise that the increased absorbance and fluorescence (and to a lesser extent, luminescence) were only evident and elicited by the combination of cells, nanoparticles and assay reagents.
Validation of magnetic nanoparticle cytotoxicity with trypan blue exclusion
Cellular reactive oxygen species production and lipid peroxidation upon magnetic nanoparticle treatment
Effect of magnetic nanoparticles on cell membrane integrity
When both the SH-SY5H and RAW 264.7 cells were incubated with the MNP-PEI-PEG nanoparticles (Figure 6B1, B2), a small but constant (and significant p > 0.05) membrane disruption was evident. The amount of LDH leakage did not appear to be concentrated or time-dependent. The cytotoxic effect was consistently less than 10%, indicating that the pegylation of the nanoparticles greatly reduced their ability to damage the cell membrane.
In this study, we successfully coated MNPs with PEI and further modified them with PEG. The zeta potential measurements for surface charge correlated well with the polymer-coupled nanoparticles [see Table S1 in Additional file 1]. Cellular uptake results [see Table S2 in Additional file 1] for both the SH-SY5Y and RAW 264.7 cells further confirmed the polymer attachment as the particles coated with the PEI and PEI-PEG had more favourable surface properties and resulted in a similar increase in cellular uptake compared to the uncoated nanoparticles.
The cytotoxicity of the polymer-coated nanoparticles was determined using three commonly used cytotoxicity assays: MTS, CellTiter-Blue and Cell-Titer-Glo (Figure 2). Our findings suggest that none of these three assays were suitable for measuring the cytotoxicity of the nanoparticles studied. In contrast to Häfeli's findings , MTS and Titer-Blue assays gave large overestimations of the cell viability in both SH-SY5Y and RAW 264.7 cells when compared to trypan blue exclusion. However, the Titer-Glo assay appeared to give the closest readings to those obtained with trypan blue exclusion (Figure 2). It is important to note that a direct comparison is not appropriate between these assays as they are testing enzyme activities in different cellular entities; however, from these results, general observations have been made.
In our experience, this phenomenon is neither unique to PEI nor to the MNPs as we obtained similar observations with other polymers (poly(L-lysine), chitosan, PEG) with homemade nanoparticles (data not shown). As apparent in our studies, the interference was reduced, but not eliminated with pegylation of the cationic polymer-coated particle. In an effort to overcome this interference, we coated wells with 0.2% w/v silica solution to prevent the polymer-coated nanoparticles from attaching to the plates . The results showed that using the 0.2% w/v silica solution did decrease the adhesive effect of the nanoparticles on the well surface; however, all three assays still overestimated the cell viability (data not shown). We hypothesised that if the MNPs were sticking to the cell membrane, then lysing cells after incubation with MTS reagents followed by centrifugation (removing cellular debris) could eliminate the interference in reading from the nanostructure. With these additional steps, the interference was reduced, but not eliminated (data not shown). We propose that for MTS and CellTiter-Blue assays, the false increase in viability might be due not only from the physical interference by the nanoparticles (not supported by our data) but also from changes in cellular activities involved in redox reactions in response to MNPs. This hypothesis merits further study.
There are many unknown factors that may influence the determination of the cytotoxicity profile of nanostructures . Recently, the EU NanoSafety Cluster group has suggested that at least four methods of determining cytotoxicity should be used in order to obtain a reliable safety profile for novel nanomaterials. The present study has suggested that for our nanoparticles, using trypan blue exclusion is the only accurate method for determining cell viability (Figure 3). Other methods which are not dependent on cellular redox activities such as [3H]-thymidine incorporation and flow cytometry should be also considered when studying nanotoxicity. We have shown a reduction in toxicity after pegylation of the MNPs, which could be due to a number of factors including an increase in the coating diameter upon addition of the PEG moiety , thus increasing the stability of the nanoparticles and further shielding the cells from the iron oxide core. The cationic charge on the PEI is decreased upon pegylation due to a reduction in the primary amines on the polymer backbone hence decreasing the cytotoxic effect on the cells . Finally, the presence of the PEG moiety may provide 'stealth' properties as has been widely reported [35–38].
In order to achieve a more in-depth understanding of the degree of cytotoxicity of the MNPs, we also investigated the effect the polymer-coated nanoparticles had on the integrity of the cell membrane and oxidative stress the MNPs elicited in cells. The ROS level increased significantly (p < 0.05) in both SH-SY5Y and RAW264.7 cells when exposed to MNP-PEI, overall in a dose-dependent manner (Figure 4). LPO in cells exhibited a similar pattern but slightly more fluctuating in SH-SY5Y cells (Figure 5). These increased ROS and LPO levels were not apparent upon incubation with MNP-PEI-PEG. The LDH leaking data showed membrane damage which was independent of nanoparticle concentrations for MNP-PEI. This is contradictory to the cell viability (Figure 3) of MNPs which was clearly dose- and time-dependent. The trypan blue and LDH assays work on the same principal, porous membranes allowing the passing of molecules. However, the size cutoff for trypan blue uptake and LDH leakage is not known, and this could account for the difference in data. We propose that a combination of oxidative stress, membrane disruption and possibly other factors contributed to the decrease of cell viability by MNP-PEI. In contrast, for MNP-PEI-PEG, the loss of cell viability over this time period could be attributed to cellular events other than oxidative stress and cell membrane damage and requires further study. As both SH-SY5Y and RAW264.7 cells possess complex functions due to their origin, other factors in both intra- and extracellular environments could be involved in the cellular responses. More studies to investigate these factors are underway in our laboratory.
Our findings show that great caution should be exercised when interpreting cell viability data from common commercial assays on novel nanoparticulates. Our data strongly suggested that nanotoxicity analysis requires a different approach compared to conventional toxicity studies used for cytotoxic drugs and other molecules which are usually much less complex and smaller than nanostructures. Our results also indicate that cell viability measurement should be complemented with analysis of other cellular events when interpreting the cytotoxicity and biocompatibility profile of nanoparticles.
aROS, LPO and LDH assays were previously checked for interferences and found to be unaffected by the nanoparticle presence. All statistical significance was assessed using t test analysis via Microsoft® Excel® 2010 (Microsoft Corporation, Redmond, WA, USA) to a 95% confidence interval.
This work was funded by the NanoSci-E+ Consortium and EPSRC UK (EP/H007040/1) (to L. Wang). All TEM images were carried out by Mr. John James in the College of Life Sciences, University of Dundee. ICP studies were carried out in the School of Pharmacy and Life Sciences, Robert Gordon University, Aberdeen. Photon correlation spectroscopy and zeta potential measurements were carried out by Mr Yousef Al-Ebini in the School of Pharmacy, University of Hertfordshire.
- McCarthy JR, Weissleder R: Multifunctional magnetic nanoparticles for targeted imaging and therapy. Adv Drug Deliver Rev 2008, 60: 1241–1251. 10.1016/j.addr.2008.03.014View ArticleGoogle Scholar
- Shubayev VI, Pisanic TR, Jin S: Magnetic nanoparticles for theragnostics. Adv Drug Deliver Rev 2009, 61: 467–477. 10.1016/j.addr.2009.03.007View ArticleGoogle Scholar
- Bulte JWM, Douglas T, Witwer B, Zhang S-C, Strable E, Lewis BK, Zywicke H, Miller B, van Gelderen P, Moskowitz BM, Duncan ID, Frank JA: Magnetodendrimers allow endosomal magnetic labelling and in vivo tracking of stem cells. Nat Biotechnol 2001, 19: 1141–1147. 10.1038/nbt1201-1141View ArticleGoogle Scholar
- Syková E, Jendelová P: Migration, fate and in vivo imaging of adult stem cells in the CNS. Cell Death Differ 2007, 14: 1336–1342. 10.1038/sj.cdd.4402140View ArticleGoogle Scholar
- Veiseh O, Gunn JW, Zhang M: Design and fabrication of magnetic nanoparticles for targeted drug delivery and imaging. Adv Drug Deliver Rev 2010, 62: 284–304. 10.1016/j.addr.2009.11.002View ArticleGoogle Scholar
- Wang YXJ, Hussain SM, Krestin GP: Superparamagnetic iron oxide contrast agents: physiochemical characteristics and applications in MR imaging. Eur Radiol 2001, 11: 2319–2684. 10.1007/s003300100908View ArticleGoogle Scholar
- Bonnemain B: Superparamagnetic agents in magnetic resonance imaging: Physiochemical characteristics and clinical applications - a Review. J Drug Target 1998, 6: 167–174. 10.3109/10611869808997890View ArticleGoogle Scholar
- Laurent S, Forge D, Port M, Roch A, Robic C, Vander Elst L, Muller RN: Magnetic iron oxide nanoparticles: synthesis, stabilization, vectorization, physiochemical characterizations and biological applications. Chem Rev 2008, 108: 2064–2110. 10.1021/cr068445eView ArticleGoogle Scholar
- Sun C, Lee JSH, Zhang MQ: Magnetic nanoparticles in MR imaging and drug delivery. Adv Drug Deliver Rev 2008, 60: 1252–1265. 10.1016/j.addr.2008.03.018View ArticleGoogle Scholar
- Häfeli OU, Riffle JS, Harris-Shekhawat l, Carmichael-Baranauskas A, Mark F, Dalley JP, Bardenstein D: Cell uptake and in vitro toxicity of magnetic nanoparticles suitable for drug delivery. Mol Pharm 2009, 6: 1417–1428. 10.1021/mp900083mView ArticleGoogle Scholar
- Fisichella M, Dabboue H, Bhattacharyya S, Saboungi M-L, Salvetat J-P, Hevor T, Guerin M: Mesoporous silica nanoparticles enhance MTT formazan exocytosis in HeLa cells and astrocytes. Toxicol in Vitro 2009, 23: 697–703. 10.1016/j.tiv.2009.02.007View ArticleGoogle Scholar
- Belyanskaya L, Manser P, Spohn P, Bruinink A, Wick P: The reliability and limits of the MTT reduction assay for carbon nanotubes-cell interaction. Carbon 2007, 45: 2643–2648. 10.1016/j.carbon.2007.08.010View ArticleGoogle Scholar
- Casey A, Herzog E, Davoren M, Lyng FM, Byrne HJ, Chambers G: Spectroscopic analysis confirms the interactions between single walled carbon nanotubes and various dyes commonly used to assess cytotoxicity. Carbon 2007, 45: 1425–1432. 10.1016/j.carbon.2007.03.033View ArticleGoogle Scholar
- Wörle-Knirsch JM, Pulskamp K, Krug HF: Oops they did it again! Carbon nanotubes hoax scientists in viability assays. NanoLett 2006, 6: 1261–1268. 10.1021/nl060177cView ArticleGoogle Scholar
- Shvedova AA, Kisin ER, Schute P, Kagan VE, Fadeel B, Castranova V: Mechanisms of pulmonary toxicity and medical applications of carbon nanotubes: two faces of Janus. Pharmacol Therapeut 2009, 121: 192–204. 10.1016/j.pharmthera.2008.10.009View ArticleGoogle Scholar
- Cheng C, Müller KH, Koziol KKK, Skepper JN, Midgley PA, Welland ME, Porter AE: Toxicity and imaging of multi-walled carbon nanotubes in human macrophage cells. Biomaterials 2009, 30: 4152–4160. 10.1016/j.biomaterials.2009.04.019View ArticleGoogle Scholar
- Monteiro-Piviere NA, Inman AO: Challenges for assessing carbon nanomaterial toxicity to the skin. Carbon 2006, 44: 1070–1078. 10.1016/j.carbon.2005.11.004View ArticleGoogle Scholar
- Davoren M, Herzog E, Casey A, Cottineau B, Chambers G, Byrne HJ, Lying FM: In vitro toxicity evaluation of single walled carbon nanotubes on human A549 lung cells. Toxicol in Vitro 2007, 21: 438–448. 10.1016/j.tiv.2006.10.007View ArticleGoogle Scholar
- Gupta AK, Gupta M: Synthesis and surface engineering or iron oxide nanoparticles for biomedical applications. Biomaterials 2005, 26: 3995–4021. 10.1016/j.biomaterials.2004.10.012View ArticleGoogle Scholar
- Figuerola A, Di Corato R, Manna L, Pellegrino T: From iron oxide nanoparticles towards advanced iron-based inorganic materials designed for biomedical applications. Pharmacol Res 2010, 62: 126–143. 10.1016/j.phrs.2009.12.012View ArticleGoogle Scholar
- Steitz B, Hofmann H, Kamau SW, Hassa PO, Hottiger MO, von Rechenberg B, Hofmann-Amtenbrink M, Petri-Fink A: Characterization of PEI-coated superparamagnetic iron oxide nanoparticles for transfection: size distribution, colloidal properties and DNA interaction. J Magn Magn Mater 2007, 311: 300–305. 10.1016/j.jmmm.2006.10.1194View ArticleGoogle Scholar
- Petri-Fink A, Steitz B, Finka A, Salaklang J, Hofmann H: Effect of cell media on polymer coated superparamagnetic iron oxide nanoparticles (SPIONs): colloidal stability, cytotoxicity and cellular uptake studies. Eur J Pharm Biopharm 2008, 68: 129–137. 10.1016/j.ejpb.2007.02.024View ArticleGoogle Scholar
- Leng Y, Sato K, Li J-G, Ishigaki T, Iijima M, Kamiya H, Yoshida T: Iron nanoparticles dispersible in both ethanol and water for direct silica coating. Powder Technol 2009, 196: 80–84. 10.1016/j.powtec.2009.07.012View ArticleGoogle Scholar
- Peng J, Zou F, Liu L, Tang L, Yu L, Chen W, Liu H, Tang J-b, Wu L-x: Preparation and characterization of PEG-PEI/Fe3o4 nano-magnetic fluid by co-precipitation method. Trans Nonferrous Met Soc China 2008, 18: 393–398. 10.1016/S1003-6326(08)60069-2View ArticleGoogle Scholar
- Vila A, Gill H, McCallion O, Alonso MJ: Transport of PLA-PEG particles across the nasal mucosa: effect of particle size and PEG coating density. J Control Release 2004, 98: 231–244. 10.1016/j.jconrel.2004.04.026View ArticleGoogle Scholar
- Jόzejczak A, Skumiel A: Ultrasonic investigation of magnetic nanoparticles suspension with PEG biocompatible coating. J Magn Magn Mater 2011, 11: 1509–1516.Google Scholar
- Douziech-Eyrolles l, Marchais H, Hervé K, Munnier E, Soucé M, Linassier C, Dubois P, Chourpa : Nanovectors for anticancer agents based on superparamagnetic iron oxide nanoparticles. Int J Nanomedicine 2007, 2: 541–550.Google Scholar
- Komuro I, Keicho N, Iwamoto A, Akagawa KS: Human alveolar macrophages and granulocyte-macrophage colony-stimulating factor-induced monocyte-derived macrophages are resistant to H2O2via their high basal and inducible levels of catalase activity. J Biol Chem 2001, 276: 24360–24364. 10.1074/jbc.M102081200View ArticleGoogle Scholar
- Mishra S, Webster P, Davis ME: PEGylation significantly affects cellular uptake and intracellular trafficking of non-viral gene delivery particles. Eur J Cell Biol 2004, 83: 97–111. 10.1078/0171-9335-00363View ArticleGoogle Scholar
- Auffan M, Rose J, Wiesner MR, Bottero J-Y: Chemical stability of metallic nanoparticles: a paramtere controlling their potential cellular toxicity in vitro. Environmental Pollution 2009, 157: 1127–1133. 10.1016/j.envpol.2008.10.002View ArticleGoogle Scholar
- Zhang S, Kucharski C, Doschak MR, Sebald W, Iludag H: Polyethylenimine-PEG coated albumin nanoparticles for BMP-2 delivery. Biomaterials 2010, 31: 952–963. 10.1016/j.biomaterials.2009.10.011View ArticleGoogle Scholar
- Fadeel B, Garcia-Bennett AE: Better safe than sorry: understanding the toxicological properties of inorganic nanoparticles manufactured for biomedical applications. Adv Drug Deliver Rev 2010, 62: 362–374. 10.1016/j.addr.2009.11.008View ArticleGoogle Scholar
- Cole AJ, David AE, Wang J, Galbán CJ, Hill HL, Yang VC: Polyethylene glycol modified, cross-lined starch-coated iron oxide nanoparticles for enhanced magnetic tumour targeting. Biomaterials 2011, 32: 2183–2193. 10.1016/j.biomaterials.2010.11.040View ArticleGoogle Scholar
- Aravindan L, Bicknell KA, Brooks G, Khutoryanskiy VV, Williams AC: Effect of acyl chain length on transfection efficiency and toxicity of polyethlyenimine. Int J Pharm 2009, 378: 201–210. 10.1016/j.ijpharm.2009.05.052View ArticleGoogle Scholar
- Moffatt S, Cristiano RJ: Uptake characteristics of NGR-coupled stealth PEI/pDNA nanoparticles loaded with PLGA-PEG-PLGA tri-block copolymer for targeted delivery to human monocyte-derived dentritic cells. Int J Pharm 2006, 321: 143–154. 10.1016/j.ijpharm.2006.05.007View ArticleGoogle Scholar
- Photos PJ, Bacakova L, Discher B, Bates FS, Discher DE: Polymer vesicles in vivo: correlations with PEG molecular weight. J Control Release 2003, 90: 323–334. 10.1016/S0168-3659(03)00201-3View ArticleGoogle Scholar
- Li S-D, Huang L: Stealth nanoparticles: high density but sheddable PEG is a key for tumour targeting. J Control Release 2010, 145: 178–181. 10.1016/j.jconrel.2010.03.016View ArticleGoogle Scholar
- Feng B, Hong RY, Wang LS, Guo L, Li HZ, Ding J, Zheng Y, Wei DG: Synthesis of Fe3o4/APTES/PEG diacid functionalised magnetic nanoparticles for MR imaging. Colloid Surface A 2008, 328: 52–59. 10.1016/j.colsurfa.2008.06.024View ArticleGoogle Scholar
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