Effects of nanoparticle size on antitumor activity of 10-hydroxycamptothecin-conjugated gold nanoparticles: in vitro and in vivo studies
Received 15 September 2015
Accepted for publication 2 February 2016
Published 7 March 2016 Volume 2016:11 Pages 929—940
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 2
Editor who approved publication: Dr Lei Yang
Hanmei Bao,1,2 Qing Zhang,2,3 Hui Xu,1,2 Zhao Yan1,2
1Department of Clinical Pharmacology, 2Key Laboratory of Cancer Prevention and Therapy, National Clinical Research Center for Cancer, 3Department of Hematology, Tianjin Medical University Cancer Institute and Hospital, Tianjin, People’s Republic of China
Abstract: Gold nanoparticles (AuNPs) have emerged as a promising anticancer drug delivery scaffold. However, some controversial points still require further investigation before clinical use. A complete understanding of how animal cells interact with drug-conjugated AuNPs of well-defined sizes remains poorly understood. In this study, we prepared a series of 10-hydroxycamptothecin (HCPT)-AuNP conjugates of different sizes and compared their cytotoxic effect in vitro and antitumor effect in vivo. Transmission electron micrographs showed that the NPs had a round, regular shape with a mean diameter of ~10, 25, and 50 nm. An in vitro drug release study showed that HCPT was continuously released for 120 hours. HCPT-AuNPs showed greater cytotoxic effects on the MDA-MB-231 cell line compared with an equal dose of free HCPT. Notably, HCPT-AuNPs of an average diameter of 50 nm (HCPT-AuNPs-50) had the greatest effect. Furthermore, administration of HCPT-AuNPs-50 showed the most tumor-suppressing activity against MDA-MB-231 tumor in mice among all treatment groups. The results indicate that AuNPs not only act as a carrier but also play an active role in mediating biological effects. This work gives important insights into the design of nanoscale delivery and therapeutic systems.
Keywords: drug delivery, cancer treatment, drug-containing nanocomposites, particle size
Over the past decade, due to their good biocompatibility, ease of synthesis, monodispersity, and tunable surface functionality,1 gold nanoparticles (AuNPs) have shown excellent potential for the delivery of a wide range of antitumor substances such as oxaliplatin,2 cisplatin,3 and paclitaxel.4 Additionally, the synthesis of AuNPs can be easily controlled to obtain NPs of a wide range of sizes.5 The size of NPs has been shown to be one of the most important factors affecting biodistribution, tissue uptake, and applications in the biomedical fields.6 It has been reported that the cellular uptake of NPs ranging from 15 to 100 nm depends upon the particle size.7 Considerable research has recently been carried out on the biodistribution, cellular uptake, and in vivo activity of AuNPs.8 NPs of a particular size (<200 nm) show efficient extravasation into leaky tumor vasculature and accumulation in tumor tissues via an enhanced permeability and retention effect.9 Particle size-dependent biodistribution and toxicity of AuNPs have been widely studied in vivo.10 Generally speaking, a smaller particle size is characteristic of higher transvascular and interstitial transport.11,12 For example, 20 nm NPs showed significantly higher permeability in tumors compared with 125 nm NPs. Therefore, to be effective, a drug carrier must be sufficiently small to perfuse out of the bloodstream, penetrate the vessels, and reach the tumor site. A type of size-shrinkable nanocarrier-based drug delivery system was developed for the inhibition of tumor growth and metastasis, with the capacity of targeting and changing size.13,14 The prepared NPs could actively target a tumor via receptor-mediated endocytosis, followed by shrinkage from a large size to a small size due to the degradation of the NPs. Current nanomedicine is focused on drug-tethered NPs of relatively larger sizes (>50 nm). To the best of our knowledge, the exact effect of size on the therapeutic performance of drug-incorporated AuNPs is still not well understood.15
Camptothecin (CPT), a natural plant alkaloid extracted from Camptotheca acuminata, a plant native to China, shows significant antitumor activity against various tumors, including lung, ovarian, breast, pancreas, and stomach tumors, via the inhibition of the activity of DNA topoisomerase I.16 Due to the promising and potent antitumor activity of CPT, many CPT derivatives have been synthesized and have received increasing attention. 10-Hydroxycamptothecin (HCPT), a natural CPT analog with a 10-hydroxy substituent, has shown stronger antitumor activity and lower toxicity in both experimental animal and human trials compared with CPT.17 It has been widely used in the treatment of gastric carcinoma, hepatoma, leukemia, and tumors of the head and neck.18 However, the therapeutic potential of HCPT has been restricted by its low aqueous solubility and instability. It has been shown that the preservation of the α-hydroxy-δ-lactone is crucial for antitumor activity.19 Unfortunately, the delivery of the lactone form is quite challenging, since the lactone ring is readily opened and converted into the carboxylate form under physiological and alkaline conditions.20 Therefore, an effective drug delivery system for HCPT is important for therapeutic purposes.
Numerous novel drug delivery systems for HCPT have been previously designed to overcome its hydrophobic and unstable characteristics. HCPT has been conjugated to poly (ethylene glycol) (PEG) to improve its water solubility. However, its therapeutic efficiency in colorectal LS174 subcutaneous tumors was not improved, due to its relatively short half-life in plasma.21 Other approaches including liposomes,22 microspheres,23 submicron emulsions,24 chitosan complexation,25 and the use of water- and lipid-soluble prodrugs26 have been proposed. However, the drug loading capacity, encapsulation, physical stability, and adverse side effects from the solubilization or encapsulation excipients are also in question. Furthermore, the relatively large size of the conjugate may limit its applications in tumor inhibition via the intravenous route.
Therefore, in this study, we report the synthesis of a series of HCPT-AuNPs for improved anticancer drug delivery that have tunable sizes from 10 to 50 nm. We wanted to add our experience with relatively small NPs to the body of this research. The NPs were characterized using transmission electron microscopy (TEM), ultraviolet–visible (UV–vis) absorption, and dynamic light scattering (DLS). We then evaluated the size-dependent uptake and cytotoxic activity of the NPs in breast cancer cells. We also investigated the antitumor effect and the tolerance to 10–50 nm HCPT-AuNP conjugates in mouse tumor xenografts.
Materials and methods
Tetrachloroauric acid (HAuCl4·3H2O), sodium borohydride (NaBH4), and sodium citrate were bought from Jiangtian Chemical Engineering Co., Ltd. (Tianjin, People’s Republic of China). HCPT and α-methoxy-poly (ethylene glycol)-ω-mercapto (PSH; Mw 5,000 Da) were purchased from Sigma (St Louis, MO, USA). Luciferase-expressing MDA-MB-231 cells (MDA-MB-231-luc) were a kind gift from Professor Niu Ruifang (Tianjin Medical University Cancer Institute and Hospital). The reagent 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) and Dulbecco’s Modified Eagle’s Medium (DMEM) were purchased from Solarbio Science & Technology Co., Ltd (Beijing, People’s Republic of China). Fetal bovine serum (FBS) was purchased from Gibco (Waltham, MA, USA).
Preparation and characterization of NPs
Synthesis of AuNPs
We synthesized a series of AuNPs of diameters of 6.4, 17.6, and 38.2 nm as measured by TEM with a JEM-100CVII instrument (JEOL, Tokyo, Japan). Synthesis of the AuNPs was accomplished by the reduction of HAuCl4 (Au3+) to neutral gold (Au0) with sodium citrate.27 Briefly, 5.0 mL of 0.1% HAuCl4·3H2O solution was added into 50 mL of double-distilled water and heated under reflux until boiling. Then, various volumes of 1% sodium citrate were added with vigorous stirring. Boiling continued for 15 minutes. By varying the sodium citrate-to-HAuCl4 concentration ratio, particles of sizes of 17.6 and 38.2 nm were obtained. An aqueous solution of NaBH4 and sodium citrate was added to the HAuCl4·3H2O solution with vigorous stirring to obtain AuNPs with diameter of 6.4 nm.
Synthesis of AuNPs containing PEG-backbones (PSH-AuNPs)
Gold nano-conjugates (PSH-AuNPs) were prepared using a single-step incubation by adding an excess of PSH to an AuNPs solution at room temperature with magnetic stirring for 2 hours. The particles were then washed three times by ultra-centrifugation at 14,000 rpm for 20 minutes. The resulting nano-conjugates were collected, lyophilized, and stored at 4°C until use.
Synthesis of HCPT-conjugated NPs (HCPT-AuNPs)
To each solution of different-sized PSH-AuNPs in distilled water (1 mL), 20 μL HCPT dissolved in dimethyl sulfoxide was added, and then the solutions were incubated at room temperature with magnetic stirring overnight. Subsequently, the solution was ultra-centrifuged at 14,000 rpm for 20 minutes three times and rinsed with 0.1 M phosphate-buffered saline (PBS) between each centrifugation. Finally, the complexes were redispersed in PBS to an appropriate volume for further study.
Characterization of NPs
UV–vis absorption spectra were recorded at room temperature using Spectra max PLUS 384 (Molecular Devices, Sunnyvale, CA, USA) in the range of 400–800 nm. NPs were placed on a copper mesh coated with an amorphous carbon film for TEM at an acceleration voltage of 100 kV to determine particle size and morphology. The zeta-potential of the NPs was measured using DLS (ZEN 3600; Malvern, UK).
For stability analysis, HCPT-AuNP conjugates and PSH-AuNPs of different sizes were incubated at 37°C under the following conditions: 0.03 M PBS at pH 7.4; and 0.03 M PBS at pH 5.5, lowered by the addition of 1 mol/L HCl, in the presence of FBS (at pH 7.4 in 0.03 M PBS solution with 2% serum) and DMEM (pH 7.4 with 10% FBS). The absorbance of the nano-conjugates was recorded at 520 nm before incubation and at 0.5, 1, 1.5, 2, 4, 6, 8, and 12 hours post-incubation. We also investigated the size variation of the nano-conjugates at predetermined time points under the conditions described.
HCPT release behavior in vitro
HCPT adsorption/conjugation onto NPs was accomplished according to the literature.28 An excess of HCPT was reconstituted in PSH-AuNPs solution and incubated at room temperature for up to 12 hours. The amount of HCPT adsorbed onto the NPs was considered to be 100% after 12-hour incubation. The mixture was then centrifuged to separate the unadsorbed HCPT from the HCPT-AuNPs conjugate. The amount of adsorbed HCPT was calculated from the difference between the initial and the free HCPT concentrations. The HCPT release behavior in vitro was studied by incubating a solution of the HCPT-AuNPs conjugate in culture medium or PBS solution containing Tween 80 (0.1%, w/v), which was placed in an air bath shaker at 150 rpm at 37°C±0.5°C. At set time intervals, samples were collected from the medium, and the same volume of fresh release medium was added. Released HCPT was separated by centrifugation, and the amount of released HCPT was determined by high-performance liquid chromatography. A reversed-phase C18 column (4.6×250 mm, 5.0 mm) was used to separate samples (20 μL injection volume). The measurement was conducted with methanol and water (55/45, v/v) at a flow rate of 1.0 mL/min and at a detection wavelength of 382 nm.
Cellular uptake of HCPT
MDA-MB-231 human breast cancer cells (2×105) were cultured in DMEM supplemented with 10% FBS in a six-well plate for 24 hours, followed by treatment with HCPT-AuNPs of different sizes for 4 hours. The solution was removed, and the cells were washed with ice-cold PBS three times and lysed by freeze-thawing and ultrasonic methods. The amount of HCPT in the cell suspension was then determined by high-performance liquid chromatography as described. Ethical permission for the human breast cancer cells use was obtained from the Ethics Committee of Tianjin Medical University Cancer Institute and Hospital.
In vitro cytotoxicity assay
The cytotoxicity of NPs of different sizes was determined by the MTT assay.29 MDA-MB-231 human breast cancer cells were cultured in the presence of DMEM supplemented with 10% FBS, penicillin (100 U/mL), and streptomycin (100 mg/mL). The cells were seeded in 96-well plates at a density of 5×103 cells per well and were allowed to attach and grow for 2 days. The cells were exposed to PSH-AuNPs, HCPT-AuNPs, or HCPT over a range of concentrations for 48 hours, and then the medium was replaced by a drug-free medium for a further 24 hours. After incubation, 20 μL of MTT solution (5 mg/mL in PBS) was added to each well and incubated at 37°C in 5% CO2 for 4 hours. The solution in the wells was then aspirated gently, and 150 μL of dimethyl sulfoxide was added to dissolve the formazan crystals. After shaking for 5 minutes, the absorbance was measured at 570 nm with a Spectra max PLUS 384 (Molecular Devices). The results were expressed as the mean percentage of cell viability relative to untreated cells.
The experimental design of this study was approved by the Ethics Committee of Tianjin Medical University Cancer Institute and Hospital. All animals were used in accordance with protocols approved by the Institutional Animal Care and Use Committee of the Tianjin Medical University Cancer Institute and Hospital. Female athymic nude mice, aged 3–4 weeks, were purchased from Institute of Laboratory Animal Sciences, Peking Union Medical College (Beijing, People’s Republic of China). Animals received a standard diet and water ad libitum.
Antitumor effects in MDA-MB-231 tumor-bearing mice
MDA-MB-231 breast carcinoma cells were cultured, harvested during log-phase growth, and resuspended in 50% matrigel. Subsequently, ~5×106 cells (0.1 mL cell suspension) were inoculated subcutaneously into the right flank of the nude mice. The tumor take rate was ~90%. The animals were examined twice weekly for the development of palpable tumors at the site of injection. The tumor volume was estimated by using the formula ab2/2, where a and b represent tumor length and width, respectively. When the average tumor volume reached 200–250 mm3, the tumor-bearing mice were randomly assigned to six groups. The negative control group was treated with saline, and the experimental groups received HCPT, PSH-AuNPs, and HCPT-AuNPs (of three different sizes), at an intraperitoneal (ip) dose of 2.0 mg HCPT/kg once daily on days 1, 5, 9, 13, and 17 (q4d×5). The tumor length and width were measured using calipers, and the tumor volume was calculated. The tumor volume was converted to tumor weight assuming that 1 mm3 was equal to 1 mg of tumor weight. The tumor volume was determined at least twice weekly for 21 days after treatment.
In vivo bioluminescent imaging
Measurement of luminescence was conducted before administration, and at 10 and 20 days post-administration using an in vivo IVIS spectrum imaging system (Caliper Life Sciences, Waltham, MA, USA). The mice were given a 150 mg/kg dose of d-luciferin by ip injection 15 minutes before imaging. General anesthesia was induced with 5% isoflurane and continued during the procedure with 2.5% isoflurane introduced via a nose cone. The data were analyzed using Xenogen Living Image® software.
The mice were weighed twice every 3 days during the study and examined for overt signs of adverse side effects related to the drug, such as appetite, diarrhea, life span, and behavior. Unacceptable toxicity was defined as a loss ≥20% of mean body weight accompanied by death of animals in the same group. After the mice were sacrificed with an overdose of sodium pentobarbital at the end of study, the heart, liver, spleen, lung, and kidney were retrieved, cut into 5 μm sections, and stained with hematoxylin and eosin, and the pathology was analyzed under a Nikon microscope (Eclipse Ti; Nikon, Tokyo, Japan).
Statistical analysis was performed using Excel 2007 and SPSS version 12.0 (SPSS Inc., Chicago, IL, USA). All values were expressed as the mean ± standard deviation (SD). Statistical significance was calculated using the Student’s t-test (within groups) or one-way analysis of variance (between groups). A value of P<0.05 was considered to be statistically significant.
Results and discussion
For the purposes of this study, we synthesized a series of HCPT-AuNP formulations with expected particle sizes of ~10, 25, and 50 nm dispersed in PBS, and characterized their properties by morphology, particle size, size distribution, and surface charge. NPs of each size have a spherical morphology with quite a narrow size distribution (Figure 1A–C). The hydrodynamic sizes obtained from the three different NPs were slightly larger than that determined by TEM because of the shrinkage of the HCPT-AuNPs during TEM sample preparation.30 In other words, the DLS determined the hydrodynamic diameter or the “equivalent sphere diameter” in solution, whereas the TEM images were obtained in the absence of a solvent.31 The zeta potential measurements show that the surface potential of the NPs was negative (Table 1). The surface plasmon of resonance band of each size of NPs was examined using UV–vis spectroscopy. The HCPT-AuNPs that we prepared showed an absorption shift from 520 to 550 nm as the size increased (Figure 1D).
To evaluate the stability of different-sized PSH-AuNPs and HCPT-AuNPs in various environments that are known to immediately induce the aggregation of unmodified AuNPs, the UV–vis absorption intensity at 520 nm was measured as a function of time, taking HCPT-AuNPs of an average diameter of 50 nm (HCPT-AuNPs-50) as an example (depicted in Figure 2A). The optical absorbance of the NPs suspension at 520 nm was slightly reduced for the HCPT-AuNPs-50 conjugate in 0.03 M PBS at pH 7.4. The relative absorbance of the groups in PBS at pH 7.4 with and without 2% serum 12 hours post-incubation was 81.8%±1.0%, and 79.4%±1.1%, respectively. The relative absorbance of the group in cell culture media was 82.6%±2.3%. Further, the relative absorbance of the group at pH 5.5 was 95.7%±0.6% at the end of the incubation time. These characteristics were likely due to a structural transformation associated with the pH change. Under acidic conditions (pH <4), HCPT exists primarily as the lactone. At physiological pH (pH 7.4), ~90% of the HCPT is in the carboxylate form.20 Furthermore, as shown in Figure 2B, the size variation of the three treatment groups was <10 nm over a period of up to 4 days, indicating that HCPT-AuNPs-50 have good stability. The results suggested that the PEG layer and HCPT conjugation effectively insulated the AuNPs from nonspecific binding to proteins and that they thus displayed satisfactory serum stability. Stability studies on HCPT-AuNPs-10, HCPT-AuNPs-25, and PSH-AuNPs were also carried out. All of the nano-conjugates had high stability, similar to that of HCPT-AuNPs-50.
Drug adsorption and release behavior in vitro
The HCPT adsorption curve depicted in Figure 3A illustrates that the interaction between HCPT and AuNPs was complete after preparation overnight. The in vitro release profile was obtained by measuring the percentage of drug released with respect to the total amount of HCPT encapsulated in the AuNPs. The release behavior of HCPT was determined at 37°C±0.5°C in culture medium or in PBS containing Tween 80 (0.1%, w/v) to mimic biological and nonbiological conditions, respectively. The release rate of HCPT from the HCPT-AuNPs conjugate in culture medium was faster than that in PBS (Figure 3B and C). These results can be attributed to the complicated composition of the culture medium that contains substances such as bovine serum albumin, vitamins, and amino acids, which contain carboxylic or thiol functional groups, as distinct from the composition of PBS.4,28 Also, we evaluated the release kinetics of HCPT for different-sized HCPT-AuNPs. All particle formulations exhibited a biphasic release profile, which was characterized by a rapid release period followed by a slower release period. Taking HCPT-AuNPs-50 as an example, ~65% of HCPT is released into the culture medium and PBS after 12 and 48 hours, respectively. After the fast release stage, HCPT was released continuously for 60 and 120 hours, reaching a percentage of cumulative release of up to 92.8%±7.3% and 72.2%±5.1% into culture medium and PBS, respectively. Further, the HCPT nano-conjugate induced a high drug release percentage of smaller sized NPs in the first 3 hours, particularly with those of a 10 nm diameter, which may be due to enhanced drug loading on the surface of the AuNPs.
MDA-MB-231 cells were treated with free HCPT or different-sized HCPT-AuNPs, and the uptake of HCPT into the cells was measured. The cells were exposed to two concentrations (100 and 200 μM) of either HCPT or HCPT-AuNPs for 4 hours (Figure 4). NPs treatment induced a significantly higher drug accumulation in the cells that was particularly obvious for HCPT-AuNPs-10. At HCPT concentrations of 100 and 200 μM, the amount of intracellular HCPT was four- and fivefold higher in the HCPT-AuNPs-10 group than in the free HCPT-treated group, respectively. Further, HCPT-AuNPs-25 accumulated at higher intracellular concentrations after 4-hour incubation compared with HCPT-AuNPs-50. Our investigation of NPs uptake by cells is similar to that observed with poly(lactic-co-glycolic acid) or other polymer NPs, and is a size- and concentration-dependent endocytic process.32,33 The smaller particles had a higher cellular internalization efficiency.34
In vitro cytotoxicity study
It has been reported that the cellular uptake of NPs ranging from 2 to 100 nm depends on their size.7,35 However, no detailed information about the uptake of different-sized drug-loaded AuNPs exists. We first evaluated the cytotoxicity of HCPT-AuNPs ranging from 10 to 50 nm in a monolayer of MDA-MB-231 cells.
The inhibitory effects of free HCPT, PSH-AuNPs, and their conjugate HCPT-AuNPs were examined in MDA-MB-231 cells using the MTT assay after 48 hours of incubation. No significant differences were seen among PSH-AuNPs of different sizes. As depicted in Figure 5A, the cytotoxicity of PSH-AuNPs on MDA-MB-231 cells at the concentration used for HCPT-AuNPs did not change with respect to the control group, suggesting that the AuNPs may be a suitable vehicle for the delivery of HCPT into cancer cells. Both the HCPT solution and HCPT nano-conjugates can significantly inhibit MDA-MB-231 cell proliferation (P<0.05). Compared with the HCPT solution, a significant increase in the inhibition rate was evident in the HCPT nano-conjugates (P<0.05). HCPT-AuNPs-50 had the highest cell inhibition effect among all the groups tested. The results were consistent with previous research that demonstrated that 50 nm citrate-stabilized AuNPs were taken up at a higher concentration than NPs of other sizes (15–100 nm).36 However, no significant difference was evident between HCPT-AuNPs-10 and HCPT-AuNPs-25. Furthermore, the HCPT solution and the HCPT nano-conjugates induced cytotoxicity in MDA-MB-231 cells in a concentration-dependent manner, as depicted in Figure 5B. The IC50 values of the nano-conjugates were much lower than that of the free HCPT solution. Taking HCPT-AuNPs-50 as an example, after 48-hour incubation, exposure to 50 and 100 μg/mL of the HCPT nano-conjugates inhibited cell growth by 26.6%±4.5% and 19.7%±2.5%, whereas in free HCPT solution, it was 69.1%±6.3% and 50.3%±4.1%, respectively. These results can be attributed to the increased solubility of HCPT by nano-conjugation. Moreover, based on the drug release measured in vitro, after 48-hour incubation, we noticed that ~73%, 77%, and 90% of HCPT was released from HCPT-AuNPs-10, HCPT-AuNPs-25, and HCPT-AuNPs-50, respectively, indicating that NPs size is a key factor that strongly impacts the drug release profile. We believe that the size is responsible for this enhanced cytotoxic effect.
It is well known that in addition to the size, the cellular uptake of NPs depends on many other factors, including the surface charge,37 the sedimentation and diffusion velocity effects of large and dense particles,38 the composition of the protein corona on the NPs,39 competition between receptors and ligands,5 and the stage of the cell cycle.40 The precise cause for the marked differences in the cytotoxicity among these three different-sized AuNPs is not clear and warrants further study.
In vivo anticancer effects in MDA-MB-231-bearing mice
We tested the in vivo antitumor efficiency of HCPT-AuNPs by ip injection into mice with subcutaneous MDA-MB-231 tumors. The median tumor size for each group as a function of time is depicted in Figure 6C and D. The growth rate of the tumors in mice treated with blank PSH-AuNPs was indistinguishable from that in the control group, indicating that the PSH-AuNPs alone had no effect on tumor growth. The group treated with free HCPT injections showed a significantly smaller tumor volume than the control group (P<0.05). The data provided strong evidence that the HCPT nano-conjugates had increased antitumor activity compared with HCPT alone. For example, the HCPT-AuNPs-25 significantly outperformed the HCPT group in this study, showing a statistically significant difference from day 5 to day 21 (P<0.05). The tumor volumes of these two groups 21 days post-drug administration were 648±87 and 905±104 mm3 (mean ± SD), respectively. These data confirmed the therapeutic effect of the HCPT nano-conjugates. HCPT injections formulated in the sodium salt of the carboxylate had only 10% of the cytotoxic activity of the lactone form.19 HCPT existed as an active lactone form in a larger percentage in the nano-conjugates, and the cellular uptake of this form might be enhanced by using HCPT-AuNPs. Several studies have reported that the active lactone form in the nanosuspensions was protected from conversion to the less potent carboxylate form in blood.18,41 The HCPT delivery system we constructed might also effectively protect the lactone form and consequently improve the activity of HCPT. Additionally, the enhanced permeability and retention effects led to preferential accumulation of HCPT-AuNPs in tumors.9 The sustained release of HCPT from the drug delivery system might provide a relatively high drug concentration in the tumor tissue. It was supposed that the drug levels in the site could reach and be maintained in the therapeutic range, resulting in increased antitumor efficiency.
In this study, we first investigated whether variations in the size of the NPs would affect the efficacy of HCPT-AuNPs in an MDA-MB-231 breast xenograft model. It is noteworthy that the HCPT-AuNPs-50 group showed the best antitumor efficiency among all of the groups. The tumor volume of the HCPT-AuNPs-50 group 21 days post-drug administration was 529±79 mm3 (mean ± SD), which was smaller than in any other group (P<0.05). Compared with the control group, injection of HCPT-AuNPs-50 started to show a statistically significant efficacy in delaying tumor growth beginning at day 5 (P<0.05 at days 9 and 13) and an even higher significant inhibition effect at days 17 and 21 (P<0.01 at days 17 and 21). Furthermore, the HCPT-AuNPs-50 group also significantly outperformed HCPT in this study, with a statistically significant difference present from day 5 to day 21 (P<0.05). Of the three different-sized drug-loaded NPs, the 50 nm NPs had the highest antitumor efficiency, which was consistent with the in vitro studies described earlier. However, no statistically significant differences were present between the HCPT-AuNPs-10 group and the HCPT-AuNPs-25 group. Size is an important parameter in a biological environment. One study has shown that NPs with diameters ~100 nm were usually distributed around tumor blood vessels, with little penetration into the tumor parenchyma.42 Previous work demonstrated that among drug-loaded polymeric micelles with diameters ranging from 30 to 100 nm, micelles ~30 nm in diameter could penetrate pancreatic tumors and achieve the best antitumor effect.11 Studies on the precise mechanisms are in progress and will be presented in a subsequent report.
Bioluminescence imaging of breast cancer growth in xenograft models
We also observed the tumor status in xenografts using a bioluminescence imaging assay. Because MDA-MB-231-luc cells implanted into mice emit photons in the presence of D-luciferin, the quantity of emitted photons measured via bioluminescent imaging precisely represents the tumor size in a living animal. Differences in the quantity of photons between the PSH-AuNPs and the control groups were not significant (P>0.05). Mice treated with HCPT or HCPT-AuNPs all showed a significant delay in tumor growth, compared with the control group (Figure 6A and B). In addition, the quantity of photons in HCPT-AuNPs-50 was the least among three different-sized HCPT-AuNPs. These data further confirm a stronger antitumor effect of HCPT-AuNPs as compared to HCPT, and further support the more potent effect in the killing of breast cancer cells of HCPT-AuNPs with diameters of 50 nm than those of 10 or 25 nm.
Pan et al43 demonstrated that the cytotoxicity of TPPMS/TPPTS-modified AuNPs depended primarily on their size and not on their ligand chemistry. They observed that AuNPs of 1–2 nm in size were highly toxic, and both smaller AuNPs and larger 15 nm gold colloids were comparatively nontoxic. Cho et al found that 13 nm PEG-coated AuNPs induced acute inflammation and apoptosis in the liver.44 These toxicity findings for PEG-coated AuNPs may have important clinical implications because PEG-coated AuNPs are widely used in biomedical applications. We evaluated the physical status of the mice by observing their appetite, fur, and behavior and found no significant difference among the six groups. Animal body weight measurement demonstrated that no obvious body weight loss was present for groups treated with different-sized HCPT-AuNPs and free HCPT throughout the study (Figure 6E). For comparison, at the end of the study, the control group and PSH-AuNPs group experienced ~16.3% and ~12.9% body weight loss, respectively. There were no disorders of the heart, liver, spleen, lung, or kidney among the groups. Representative hematoxylin and eosin staining photomicrographs are shown in Figure 7. No overt, concomitant signs of toxicity were observed.
Our work provides new insights into the function of different-sized HCPT-loaded AuNPs, ranging from 10 to 50 nm. The NPs showed a steady and sustained release profile in vitro up to 120 hours. The 50 nm HCPT-loaded AuNPs had unique advantages over smaller NPs in terms of killing MDA-MB-231 cells and therapeutic performance in a tumor xenografted mouse model. In conclusion, this drug delivery system is an effective strategy for achieving the improvement of the therapeutic efficacy of anticancer drugs. Furthermore, our results suggest that drug-loaded AuNPs can be designed and functionalized to achieve improved antitumor efficacy by optimizing the particle size.
We thank Prof Ruifang Niu (Tianjin Medical University Cancer Institute and Hospital) for the gift of the MDA-MB-231-luc cells. This work was supported by National Science and Technology Major Project (No. 2013ZX09303001) and Tianjin Medical University Cancer Institute and Hospital fund (No. B1205).
Zhao Yan and Hanmei Bao designed the research. Hanmei Bao, Qing Zhang, and Hui Xu undertook the research. Hanmei Bao and Qing Zhang analyzed the data. Zhao Yan and Hanmei Bao wrote the paper. All authors contributed toward data analysis, drafting and critically revising the paper and agree to be accountable for all aspects of the work.
The authors report no conflicts of interest in this work.
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