Synthesis and Cytotoxicity of Y2O3 Nanoparticles of Various Morphologies
© to the authors 2009
Received: 8 June 2009
Accepted: 24 September 2009
Published: 24 November 2009
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© to the authors 2009
Received: 8 June 2009
Accepted: 24 September 2009
Published: 24 November 2009
As the field of nanotechnology continues to grow, evaluating the cytotoxicity of nanoparticles is important in furthering their application within biomedicine. Here, we report the synthesis, characterization, and cytotoxicity of nanoparticles of different morphologies of yttrium oxide, a promising material for biological imaging applications. Nanoparticles of spherical, rod-like, and platelet morphologies were synthesized via solvothermal and hydrothermal methods and characterized by transmission electron microscopy (TEM), X-ray diffraction (XRD), light scattering, surface area analysis, thermogravimetric analysis (TGA), and zeta potential measurements. Nanoparticles were then tested for cytotoxicity with human foreskin fibroblast (HFF) cells, with the goal of elucidating nanoparticle characteristics that influence cytotoxicity. Cellular response was different for the different morphologies, with spherical particles exhibiting no cytotoxicity to HFF cells, rod-like particles increasing cell proliferation, and platelet particles markedly cytotoxic. However, due to differences in the nanoparticle chemistry as determined through the characterization techniques, it is difficult to attribute the cytotoxicity responses to the particle morphology. Rather, the cytotoxicity of the platelet sample appears due to the stabilizing ligand, oleylamine, which was present at higher levels in this sample. This study demonstrates the importance of nanoparticle chemistry on in vitro cytotoxicity, and highlights the general importance of thorough nanoparticle characterization as a prerequisite to understanding nanoparticle cytotoxicity.
Interest in nanoparticles for biological and medical applications continues to grow. Nanoparticles find use as delivery vehicles for drugs [1, 2], genes [3, 4], and growth factors , as well as cellular labels for imaging both in vitro and in vivo [6–8]. Nanoparticles are also being studied for use in photodynamic therapy (PDT)  and hyperthermia therapy for tumors , with the goal of clinical applications. Organic nanoparticles, such as polymeric or protein nanoparticles, and inorganic nanoparticles, such as gold and semiconductor nanoparticles, are being investigated for these applications. Clearly, for any biological or medical application of nanoparticles, biocompatibility of the nanoparticles is imperative.
Nanoparticles can disrupt and impair normal cellular function through a number of different mechanisms . First, nanoparticles may be comprised of toxic materials or ions that poison the cells, or materials that generate free radicals, such as reactive oxygen species (ROS). For example, some metal and semiconductor nanoparticles, such as CdSe or CdTe, are known to be cytotoxic to a variety of cells [12, 13]. This is in part due to material decomposition and release of toxic Cd2+ ions, which bind to sulfohydryl groups of mitochondria protein, causing mitochondrial dysfunction and cellular poisoning . Material decomposition is of greater likelihood for nanoparticles than bulk material due to their enhanced surface area to volume ratio. Generation of free radicals following excitation and photooxidation of CdTe nanoparticles has also been observed to contribute to cytotoxicity . Cytotoxicity due to ROS generation has been reported with a number of different nanoparticles, including TiO2, C60, and CeO2. Second, regardless of composition, the nanoparticles may adhere to cell membranes or pass through the membrane and become internalized within the cell, which may impair cellular functions [11, 19]. For example, charged nanoparticles enter cells through the creation of pores in the cellular membrane , a phenomenon associated with cytotoxicity. Third, the morphology of the nanoparticle may disrupt the cellular membrane, as in the case of carbon nanotubes that have reportedly speared cells like lancets, killing them [21, 22].
Altering nanoparticle characteristics such as size, surface chemistry, phase, and morphology can tune the earlier mentioned cytotoxicity mechanisms, potentially resulting in greatly different cytotoxicity responses for materials of essentially the same composition. For example, CdTe nanoparticles of different sizes display different degrees of cytotoxicity, due in part to differences in cellular uptake and cell internalization pathways, which are dictated by size . Polystyrene nanoparticles functionalized with NH2 on their surface were markedly more cytotoxic than bare polystyrene nanoparticles or COOH-functionalized polystyrene nanoparticles, due to increased cellular uptake . Anatase phase TiO2 nanoparticles are reportedly 100 times more toxic than equivalent size and shape rutile phase TiO2 nanoparticles, due to changes in exposed surface atoms which render the anatase phase more efficient at generation of ROS . Carbon nanoparticles of different morphologies (spheres, multiwalled spheres, nanotubes, multiwalled nanotubes) were found to have different degrees of cytotoxicity [26, 27]. It was concluded from these results that the cells responded differently according to the shape of the nanomaterials. In another study, spherical Au nanoparticles were not found to be toxic to human skin cells, while Au nanorods synthesized from the Au nanoparticles via a seed mediated, surface assisted growth method were observed to be highly toxic . Whether the nanoscale geometry plays a role here was not clear, as this was attributed to the presence of hexadecylcetlytrimethylammonium bromide (CTAB), a surfactant used to stabilize the nanorods that is not present on the nanoparticles. A study of Pt nanoparticles of different morphologies reported that surface area and oxidant reactivity of certain morphologies increased cellular uptake (~1.5 times greater) and increased retention in lung tissue when compared to other morphologies . In fact, surface area was highlighted as being an important nanoparticle characteristic for studying and predicting the toxicology of nanoparticles by The European Centre for Ecotoxicology and Toxicology of Chemicals .
In light of these studies, we report here on the synthesis and characterization of various yttrium oxide nanoparticle morphologies to assess cytotoxicity and reactive oxygen species (ROS) generation, with the aim of determining the nanoparticle characteristics that are important in designing biocompatible nanoparticles. Such correlations are currently lacking for yttrium oxide nanoparticles. We hypothesize that different yttrium oxide powder characteristics will have different cytotoxicity responses and different ROS generation levels and that characterization will reveal the specific nanoparticle characteristics that govern the cytotoxicity responses in this system.
Yttrium oxide, Y2O3, a widely used host material for various rare earth dopants, is of interest for potential applications in biological imaging, as well as photodynamic therapy [31–33]. Yttrium and the rare earth element commonly doped (Yb, Er, Eu) into yttrium oxide are not known to be cytotoxic, making yttrium oxide a better candidate than the quantum spherical nanoparticle chemistries for in vivo applications. Cubic phase yttrium oxide possesses a low phonon energy of 380 cm−1, which makes it a good host for upconversion, i.e., emission of a lower wavelength photon, such as in the visible range, upon excitation with a longer wavelength photon, typically in the near infrared (NIR) range [34–36]. This is of particular interest in biological imaging, as the main absorbers in tissue, namely water, hemoglobin, and melanin, have minimal absorption in the NIR . Thus, use of nanoparticles with excitation in the NIR wavelengths would allow for deeper penetration of excitation photons for deep tissue imaging applications. Additionally, it has been reported that monoclinic yttrium oxide nanoparticles can protect cells from oxidative stress ; however, this has not been studied with cubic phase Y2O3, which possesses superior upconversion properties and is therefore of greater interest for biological imaging applications .
Yttria and yttrium oxide precursors have been prepared by a number of synthetic methods. Combustion synthesis has been used by different groups to prepare nanoparticles and nanocrystalline powders of yttrium oxide [35, 40–43]. Solvothermal and hydrothermal synthesis [44–48], precipitation techniques [49–55], and thermal decomposition methods [56, 57] are also widespread methods for preparation of Y2O3. A variety of nanoparticle morphologies for yttrium oxide, including spherical nanoparticles [58–61], nanorods , nanowires , nanotubes [48, 62], and nanodisks [56, 57], have been synthesized from different methods. Morphological control over Y2O3 nanoparticles has been achieved with hydrothermal synthesis by varying pH, but the resulting nanorods and nanoflakes had lengths and lateral dimensions, respectively, on the order of microns . Wire-like and spherical morphologies of Y2O3 were synthesized by a solvothermal method by varying solvent composition . Zhang et al.  reported morphological evolution of spherical nanoparticles into nanorods via oriented attachment in long chain alkylamine solvents. Here, we report a new synthesis method to make novel Y2O3 nanoparticles with a square platelet morphology. Although there are many reports on the synthesis and upconversion properties of yttrium oxide nanoparticles, there are few reports on the cytotoxicity or biocompatibility responses of nanoparticles varying morphology [38, 63]. We characterize the samples by a variety of techniques, and then use these nanoparticles to assess in vitro cytotoxicity, in order to study which nanoparticle characteristics govern cytotoxicity in this system.
Nanoparticle characteristics and measurement methods
30 × 150
Crystallite size (nm)
Surface area (m2/g)
Size (nm), spherical shape factor
Size (nm), morphology shape factor
Carbon analysis (wt%)
Ligand coverage (molecules/nm2)
Zeta potential (mV)
DLS (μm) volume weighted mean
SLS (μm) volume weighted mean
Yttrium (III) acetate hydrate 99%, technical grade oleylamine 70%, reagent grade ammonium hydroxide 30%, yttrium (III) nitrate hexahydrate 99.8%, ethylene glycol anhydrous 99.8%, reagent grade ethanol 99.5%, reagent grade methanol 99.8%, reagent grade chloroform 99.8%, and reagent grade hexanes 98.5% were all purchased from Sigma–Aldrich (St. Louis, MO) and used without further purification.
Square platelets and spherical nanoparticles were synthesized by a modification of the solvothermal decomposition method developed by Si et al. . In a standard synthesis, 0.5 mmol of yttrium acetate was dissolved in 30-mL oleylamine in a three-neck flask. The solution was stirred and degassed under vacuum at ~70 °C until bubbling stopped, typically 5–10 min. The degassed solution was then rapidly heated to 310 °C. At approximately 150 °C, the clear yellow solution turned cloudy white, indicating the nucleation of nanoparticles. The solution was held at 310 °C for 30 min, after which an ~ 5 mL aliquot (referred to as A1, spherical nanoparticles) was then removed from the solution to follow morphological evolution of the nanoparticles. Subsequently, an additional 0.5 mmol of yttrium acetate dissolved in 5-mL oleylamine was slowly dripped in to the solution at a rate of 1 mL/min. Immediately after all solution had dripped in, a second ~5 mL aliquot (A2) was removed. The reaction was allowed to continue for 15 min, after which a third aliquot of ~5 mL (A3) was removed. The reaction was allowed to proceed for an additional 15 min (product, platelets), after which heating was stopped. Nanoparticles were kept in the reaction solution and precipitated and washed as needed. The washing method depended upon the characterization technique employed, as detailed in the section “Nanoparticle Characterization”.
To have an additional nanoparticle morphology for cytotoxicity testing, Y2O3 nanoparticles of rod-like morphology were synthesized hydrothermally in ethylene glycol in water solvent mixture by a previously published method reported by Yin et al. . Briefly, 150 mL of 0.2 M Y(NO3)3 aqueous solution was added to 200 mL of ammonium hydroxide. The resulting precipitate was centrifuged at ~6,000 RCF (Relative Centrifugal Force) for 5 min and washed with water 3 times, then resuspended in 60 mL of ethylene glycol. The solution was placed into a Teflon liner and hydrothermally reacted in a 160-mL Parr bomb Series 4760 filled to 80% volume capacity (Parr Instrument Co., Moline, IL) for 5 h at 250 °C. The reaction product was precipitated and washed as described earlier.
To study size and morphological evolution of the nanoparticles prepared by solvothermal and hydrothermal methods, transmission electron microscopy (TEM) was employed. To prepare TEM samples, nanoparticles were precipitated from the reaction solution by centrifugation at ~6,000 RCF for 5 min (Beckman Coulter Avanti J-26 XP, Fullerton, CA), then washed by resuspension in ethanol and precipitated by centrifugation at ~3,000 RCF for 5 min. The precipitate was resuspended in chloroform or hexanes, and the solution was diluted until no longer turbid. A drop of dilute nanoparticle suspension was deposited onto a 400-mesh Formvar-backed carbon grid (Electron Microscopy Sciences, Hatfield, PA), dried at room temperature under vacuum for 24 h, and imaged at 125 kV with a JEOL 100cX TEM (Tokyo, Japan).
where d is crystallite diameter, λ is the wavelength of the X-rays, B is the peak breadth of the XRD peak, and θ B is the Bragg angle (in radians). B and θ B were determined by fitting the peaks in the XRD spectra with Gaussian and Lorentzian peaks using Origin 7.5 software (OriginLab Corp, Northampton, MA). Reported sizes were averaged from the sizes calculated using each peak fit across all distinguishable peaks in the XRD spectrum.
where D e is an equivalent diameter of a sphere with the same volume as the particle, A is the surface area of the particle, and V is the volume of the particle. A theoretical density value for single crystalline cubic Y2O3 of 5.028  was used for calculations. As density has been shown to decrease as particle size moves to the nanoscale domain, a calculated nanoparticle density based on a core/shell model was also used for comparison .
Fourier Transform Infrared Spectroscopy (FT-IR) was performed to probe the chemical nature of the nanoparticle surface. For FT-IR measurements, nanoparticles were precipitated from the reaction solution and washed as described for nitrogen isotherms. Samples were dried as described earlier for XRD measurements. Diffuse transmission FT-IR spectra for the powders were recorded at room temperature with a Galaxy Series 5000 FT-IR (Madison Instruments Inc., Middleton, WI).
To determine the amount of water or oleylamine remaining on washed and dried nanoparticle powders, thermogravimetric analysis (TGA) was performed, as well as carbon analysis. Nanoparticles were precipitated from the reaction solution and washed as described earlier for nitrogen isotherms. Samples were dried as described earlier for XRD measurements. TGA was performed with a Perkin Elmer TGA 7 LoTemp (Perkin Elmer, Waltham, MA) under air flowing at a rate of 20 mL/min. Samples were heated from room temperature to 100 °C and held at this temperature for 90 min, then ramped to 800 °C at a rate of 25 °C/min and held for 90 min at 800 °C. Carbon analysis by combustion was conducted by Robertson Microlit Laboratories, Madison, NJ.
Nanoparticle stock suspensions were prepared by washing and drying nanoparticle samples as described earlier for TGA, and dispersing a known weight of nanoparticles in deionized water via ultrasonication (Fisher Scientific Ultrasonicator FS60, Pittsburgh, PA) for 45 min, to achieve a concentration of 10 mg/mL. These stock suspensions were used for characterization and testing as described later. Because the as-synthesized nanoparticles dispersed poorly in water and tended to agglomerate, if the stock suspensions had been sitting for more than a day, they were sonicated for 30 min immediately prior to any testing. No surface modification was performed in order to test the cytotoxicity of native nanoparticles without convoluting effects from surface functionalization. Agglomerate size was measured using dynamic light scattering (Brookhaven Instruments Zetapals Particle Size Analyzer, Holtsville, NY; 3 scans, 3 runs/scan, 60 s/run) and static light scattering (Beckman Coulter, Coulter LS 230, Fullerton, CA, 3 runs, 60 s/run). Zeta potential was calculated from electrophoretic mobility determined via phase analysis light-scattering measurements with a Brookhaven Instruments Zetapals Particle Size Analyzer using the Smoluchowski model  (Holtsville, NY, 3 scans, 3 runs/scan, 30 s/run).
Human foreskin fibroblasts (HFF) were isolated from circumcision samples and expanded. Fibroblast cells were chosen for cellular tests because they are a widely accepted model cell type used for cytotoxicity testing . Cells were grown in T25 (Becton–Dickson, Franklin Lakes, NJ) or T75 flasks (Corning Corp., Corning, NY) with McCoy’s 5A Media (Gibco, Carlsbad, CA) supplemented with 1% l-glutamate (Invitrogen, Carlsbad, CA), 10% fetal bovine serum (Gibco, Carlsbad, CA), and 1% penicillin–streptomycin (Lonza, Walkersville, MD). For cytotoxicity testing, cells were passaged with Trypsin–EDTA (Lonza, Walkersville, MD) and reseeded into 96-well tissue culture polystyrene plates (Becton–Dickson, Franklin Lakes, NJ). Cells were allowed to attach and grow to ~80–90% confluency (density) for cytotoxicity testing. Nanoparticle test suspensions were prepared by diluting an appropriate volume of stock suspension in complete media to achieve desired testing concentrations (from 25 to 500 μg/mL).
For cytotoxicity tests, media was removed from cells plated in 96-well plates and replaced with nanoparticle-enriched media. At least 6 replicates per sample were tested. After 24 h, wells were washed with PBS and stained with calcein AM (Invitrogen, LIVE/DEAD Cytotoxicity Kit for Mammalian Cells, Carlsbad, CA). Non-fluorescent calcein AM enters the cells, and is converted to fluorescent calcein in the presence of esterase activity, thus staining only live cells. Cells were also stained with ethidium homodimer (Invitrogen, LIVE/DEAD Cytotoxicity Kit for Mammalian Cells, Carlsbad, CA), which cannot penetrate intact cell membranes, thus staining only dead cells. Due to washing steps conducted before the assay, most dead cells were washed off the wells, rendering the readings of the ethidium homodimer stain similar for all test conditions and controls. Therefore, only the calcein fluorescence data were used. Plates were read on a fluorescent plate reader (Applied Biosystems, Cytofluor Series 4000, Foster City, CA). Microsoft Excel was used to perform t-testing for statistical analysis of the data.
Reactive oxygen species (ROS) generation of the nanoparticles without cells was tested by adding dichlorofluorescein diacetate (Sigma–Aldrich, St. Louis, MO) to 100 μg/mL of nanoparticles in PBS. When non-fluorescent dichlorofluorescein diacetate becomes oxidized, it becomes fluorescent. Sample fluorescence was read with a fluorescence plate reader (Applied Biosystems, Cytofluor Series 4000, Foster City, CA).
In order to understand the underlying nanoparticle characteristics that are responsible for cytotoxicity in a given system of nanoparticles, thorough characterization of the nanoparticle samples is key. Therefore we employed a variety of characterization methods to study the particle size, morphology, phase, crystallite size, surface chemistry and area, and agglomeration of the different nanoparticle samples in aqueous solution. It is important to not only characterize the nanoparticle powders, but to also characterize the nanoparticles in aqueous solution, as the samples must be in aqueous solution for cytotoxicity testing.
Oriented attachment of spherical nanoparticles into nanorods has been noted before for yttrium oxide . Zhang et al.  report monodisperse Y2O3 nanoparticles that form chain-like agglomerates due to van der Waals interactions, which then cement and reshape into nanorods. A similar mechanism can be used to explain the morphological evolution of the square nanoplatelet presented here. First, spherical nanoparticles form, (Fig. 2a), which then agglomerate into a tangle of wires upon the addition of more precursors into the reaction solution (Fig. 2b). These then begin to grow laterally, producing ribbons (Fig. 2c). These intermediate morphologies were not chosen for cytotoxicity testing due to their large (order of microns) length scales, and the fact that they are comprised of associated individual spherical nanoparticles. The interactions that cause the nanoparticles to agglomerate into the observed transitional morphologies during the reaction are not strong enough to keep the morphologies stable in the presence of many charged species, as found in cell culture conditions. The spherical nanoparticles that comprise the ribbon structures then coalesce and reform into square platelets or sheets. Wang et al. have noticed the formation of Lu2O3[71, 72] square platelets from spherical nanoparticles under hydrothermal conditions. The addition of more precursors was crucial for the square platelet morphology. If the reaction was carried on for 1 h at 310 °C without addition of more precursors, only spherical nanoparticles formed. Furthermore, if precursors were dripped into the solvent at 310 °C without any existing precursors present, only spherical nanoparticles formed.
Crystallite sizes calculated from the peak broadening, listed in Table 1, were 3 nm for the spherical nanoparticle sample, 4 nm for the platelet sample, and 11 nm for the rod-like sample. Discrepancies between TEM and XRD calculated sizes of particles can be due to differences in size distributions captured by the different techniques, as well as polycrystallinity of the particles. Based on our SAED (discussed earlier), the size discrepancy here appears due to the polycrystalline nature of the platelet and rod-like particles. Additionally, the differences in sizes (e.g., 33 nm diameter and 150–200 nm length for rods as measured via TEM vs. XRD calculated size of 11 nm) are too large to be attributed to differences in size distributions. The fact that these particles are polycrystalline means they are comprised of randomly oriented crystallites, and there is no preferred crystallographic orientation, which could possibly be the case if the rod or platelet particles were single crystals.
The surface area as determined by nitrogen isotherms was 150 m2/g for the spherical nanoparticles, 109 m2/g for the platelet sample, and 93 m2/g for the rod-like nanoparticles. Due to the large dimensions of the rods, this sample has the smallest specific surface area, while the 5-nm spherical nanoparticles have the largest specific surface area because of their small size. XRD of the samples, post-degassing, did not exhibit any reduction in peak broadening, indicating that the degassing procedure did not cause significant crystal growth. Particle size (see Table 1) calculated from the specific surface area, using the single crystal density value of 5.028, with a shape factor (K s ) of 6 (spherical), was 8 nm for the spherical nanoparticles, 11 nm for the platelet sample, and 13 nm for the rod-like nanoparticles. Accounting for non-spherical morphologies by using a calculated K s of 8.6 (aspect ratio = 5) for the rods and 25 (aspect ratio = 28) for the platelets gives a calculated particle size of 18 and 45 nm, respectively. These particle sizes are still significantly smaller than those observed via TEM (150 and 140 nm, respectively), indicating that perhaps the single crystal density value is not an appropriate choice for these particles; therefore, particle sizes were calculated using a calculated density value obtained by assuming a core of yttrium oxide and a shell (surface) layer of oleylamine through a model developed by Lojkowski . The model gives sizes closer to those seen with TEM (e.g., 70 nm for the platelet), indicating that the samples probably have a lot of ligand present, reducing their density. The sizes are still not reconcilable, though, which can be due to particle size distributions not seen via TEM and not knowing the precise particle density considering how organics coat the particle surfaces.
FT-IR data indicate that the spherical nanoparticle and platelet samples are coated with a “shell” of oleylamine. Peaks are observed at ca 2,930 and 2,850 cm−1, corresponding to C–H stretching, and peaks at ca 1,060, 950 cm−1 corresponding to =C–H out of plane and in plane bending  or NH2 bending modes . All match the spectra of pure oleylamine. In contrast, the rod-like sample coated with ethylene glycol has a broad OH peak ca 3,375 cm−1 and a C–H stretch of 2,830 cm−1 and asymmetric and symmetric glycolate stretches (less like C–H bends) at 1,380 and 1,620 cm−1. These FT-IR results are as expected; samples synthesized in oleylamine are coated with oleylamine, and the sample synthesized in ethylene glycol is coated with ethylene glycol.
Zeta potentials for all aqueous nanoparticle suspensions were highly negative, with spherical nanoparticles having an average zeta potential of −13 mV, the platelets having an average zeta potential −27 mV, and the rods having an average zeta potential −28 mV. The volume weighted mean agglomerate size of all aqueous nanoparticle suspensions as measured by dynamic light scattering was ~1.5μ. However, this size is actually beyond the range of sizes than can reliably be determined with dynamic light scattering. Therefore, static light scattering was performed for a more accurate determination of agglomerate size. As determined from static light scattering, the volume weighted mean size for the spherical nanoparticles was 0.7 μm, the platelet sample was 0.7 μm, and the rod-like sample was 0.8 μm. This agglomerate size is larger than seen in the TEM images, but this is to be expected, as the TEM samples were prepared from nanoparticles suspended in organic solvents, where they disperse much better.
In summary, the characterization data (Table 1) establish that the nanoparticle samples are of similar crystal phase, crystallite size, zeta potential, and agglomerate size in aqueous media and that the platelet and rod-like samples are polycrystalline. The particles differ in surface area, morphology, particle size, amount of ligand present per weight of sample, and degree of ligand coverage. Once the characteristics of the nanoparticle samples were studied, samples were then tested for cytotoxicity with cells, with the goal of assessing the nanoparticle characteristics that affect cytotoxicity.
Determining the source of the observed differences in ROS generation and cytotoxicity requires a careful analysis of the characterization data. One would expect the ROS generation and cytotoxicity to correlate to a surface characteristic of the nanoparticles (area, chemistry, etc.), as the surface of the nanoparticles is what is exposed to cells and what is available to react and form ROS. Based on the characterization data, ROS levels surprisingly do not correlate with specific surface area, as the spherical sample possessed the largest specific surface area but did not generate the highest levels of ROS. It is also clear that the ROS generation of the platelets is not a result of the particle size, as the rod-like nanoparticles possess similar lengths but did not generate as much ROS. Both the platelet and rod-like samples are polycrystalline, and as such, they are comprised of randomly oriented crystallites without preferred crystallographic orientation. Therefore, the surface of these particles, aside from the capping ligand, is similar, and cannot be the cause of the observed cytotoxicity response. Additionally, agglomerate size in aqueous solution, zeta potential, and crystal phase of all samples were similar, so these characteristics cannot be affecting ROS generation levels. The most significant difference between samples that can be correlated to the ROS generation and cytotoxicity is the surface chemistry of the samples. The platelet sample has elevated levels of surface coverage of oleylamine relative to the spherical sample, as calculated from the carbon analysis and surface area data. Although the rod-like sample had a higher level of surface coverage, it is coated with ethylene glycol, which is seemingly less toxic to cells than oleylamine . The characterization data therefore seem to point to the oleylamine in the platelet sample as the cause of the observed cytotoxicity.
In conclusion, we have synthesized and characterized yttrium oxide nanoparticles of spherical, platelet, and rod-like morphology, and explored the cytotoxicity of these different nanoparticles. Spherical nanoparticles had no effect on cell viability up to the maximum tested concentration of 500 μg/mL, and rods enhanced cell proliferation at concentration of 100 μg/mL and above. Platelets were cytotoxic to HFF cells at concentrations of 50 μg/mL and above, which in part may be due to the increased ROS generation observed from this sample. Based on the nanoparticle characterization, the increased ROS generation is attributed to the stabilizing ligand oleylamine, which has a higher degree of surface coverage in the platelet sample than the spherical sample. While the rod-like sample had a degree of surface coverage similar to the platelets, it was coated with ethylene glycol, not oleylamine. Therefore, in this system, the surface chemistry of the nanoparticles is the characteristic that appears to govern the cytotoxicity responses. These cytotoxicity results also indicate that it is important to thoroughly characterize nanoparticle samples by a variety of methods in order to understand and properly correlate observed cytotoxicity with the correct nanoparticle characteristic. Once the true underlying nanoparticle characteristic giving rise to the observed cellular response has been determined, it may be possible to tune cytotoxicity by adjusting, either during or post-synthesis, the nanoparticle characteristic that has been pinpointed.
This work was supported in part by the National Science Foundation NIRT Grant 0609000 and in part by Grant Number T32EB005583 from the National Institute Of Biomedical Imaging And Bioengineering. The content is solely the responsibility of the authors and does not necessarily represent the official views of the National Institute Of Biomedical Imaging And Bioengineering or the National Institutes of Health.