RNA interference (RNAi) is a powerful approach for silencing genes associated with a variety of pathologic conditions; however, in vivo RNAi delivery has remained a major challenge due to lack of safe, efficient, and sustained systemic delivery. Here, we report on a novel approach to overcome these limitations using a multistage vector composed of mesoporous silicon particles (stage 1 microparticles, S1MP) loaded with neutral nanoliposomes (dioleoyl phosphatidylcholine, DOPC) containing small interfering RNA (siRNA) targeted against the EphA2 oncoprotein, which is overexpressed in most cancers, including ovarian. Our delivery methods resulted in sustained EphA2 gene silencing for at least 3 weeks in two independent orthotopic mouse models of ovarian cancer following a single i.v. administration of S1MP loaded with EphA2-siRNA-DOPC. Furthermore, a single administration of S1MP loaded with-EphA2-siRNA-DOPC substantially reduced tumor burden, angiogenesis, and cell proliferation compared with a noncoding control siRNA alone (SKOV3ip1, 54%; HeyA8, 57%), with no significant changes in serum chemistries or in proinflammatory cytokines. In summary, we have provided the first in vivo therapeutic validation of a novel, multistage siRNA delivery system for sustained gene silencing with broad applicability to pathologies beyond ovarian neoplasms. Cancer Res; 70(9); 3687–96. ©2010 AACR.
RNA interference (RNAi) therapy is emerging as a treatment modality of exceptional promise, in view of its versatile application to the silencing of any gene with a known sequence and especially those that are not drugable by existing approaches such as small-molecule inhibitors. However, in vivo systemic administration of RNAi has remained a major challenge due to its short half-life (1), lack of ability to penetrate the plasma membrane (2), and potential toxicity (3, 4). Nanoparticle-based delivery systems have been proposed to address these concerns. The validity of RNAi therapeutics has been shown in animal models (3, 5–7) and more recently in human clinical trials (8, 9). For all of the potential small interfering RNA (siRNA) delivery advantages they engender, nanoparticles also have some limitations including their potential for rapid clearance (10), instability in serum (11), and systemic toxicity, especially to the liver (3). Moreover, most of the current RNAi delivery approaches require frequent injections (12, 13), which can be a substantial impediment to patient treatment due to impaired enrollment on clinical trials and decreased patient compliance (14). Thus, development of safe, easy to administer, and efficient delivery systems that achieve sustained target gene silencing is of substantial clinical importance.
Previously, we have shown that siRNA incorporated in neutral nanoliposomes (30–40 nm in diameter) composed of dioleoyl phosphatidylcholine (DOPC) led to therapeutic gene modulation in several orthotopic cancer models with no overt toxicities (12, 13). Although our lipid-based siRNA delivery platform holds substantial promise for clinical translation, as is the case for other nanocarriers, our method currently requires twice weekly injections to achieve continuous gene silencing. We sought to develop a biocompatible approach that would allow for the sustained delivery of siRNA resulting in continuous gene silencing, therapeutic efficacy at nontoxic doses, and ease of administration. To attain these goals, we have developed a multistage delivery approach (Fig. 1A) composed of two biodegradable and biocompatible carriers: the first-stage carriers are mesoporous microscale biodegradable silicon particles (stage 1 microparticles: S1MP; ref. 15), allowing for the loading and release of second-stage nanocarriers (DOPC nanoliposomal siRNA: siRNA-DOPC) in a sustained manner. Here, we provide the first evidence that a single administration of multistage siRNA-DOPC delivery resulted in sustained in vivo gene silencing for 3 weeks, significant antitumor effect in two orthotopic mouse models of human ovarian cancer with no observable concurrent toxicity.
Materials and Methods
Fabrication of porous silicon particles
Porous silicon particles were fabricated by electrochemical etching of silicon wafers as previously described (15). The physical dimension and pore size of S1MP were verified by high-resolution scanning electron microscope. The porosity was verified by nitrogen absorption analysis as previously described (15).
Surface chemistry of S1MP
Surface of the S1MP was hydroxylated in oxygen plasma (O2100sccm 50W). The positively charged amine groups were introduced on the surface by silanization with 9% v/v 3-aminopropyltriethoxysilane in isopropanol as previously described (15). The surface charge was measured by Zeta Pals (Brookhaven Instruments).
Liposomal siRNA formulation
The siRNA liposomes were prepared as previously described (13) by mixing 1,2 dioleoyl-sn-glycero-3-phosphocholine with siRNA (20:1, mol/mol) in the presence of excess t-butanol. Control siRNAs (5′-AATTCTCCGAACGTGTCACGT-3′) and Alexa 555–tagged control siRNA were purchased from Qiagen and siRNAs against EphA2 (5′-AATGACATGCCGATCTACATG-3′) were purchased from Sigma (16). Dry film of DOPC liposomes were reconstituted by adding water followed by briefly sonication.
Assembly of multistage vector
Amino functionalized S1MP (1 × 107 particles, 5 μg silicon) were mixed with t-butanol, and dried and mixed with DOPC nanoliposomes containing fluorescently labeled siRNA. The mixture was briefly sonicated and then spun down to remove any unincorporated free DOPC-siRNA. Fluorescence intensity of the supernatants as well as the precipitants were measured at Ex 555/Em 592 to assess loading efficacy.
Cell lines and culture
The human epithelial ovarian cancer cell lines such as HeyA8-Lc and Skov3ip1-Lc were used for these studies. Cells were maintained in RPMI 1640 supplemented with 15% fetal bovine serum and 0.1% gentamicin sulfate as described as previously (13). All experiments were performed with 70% to 80% confluent cultures.
Orthotopic in vivo model of ovarian cancer and tissue processing
Female athymic nude mice (NCr-nu; 4- to 5-week-old) were purchased from Taconic Farms and maintained as previously described (13). Institutional Animal Care and Use Committee approval was obtained before all animal studies. All mouse studies were approved by the M.D. Anderson Cancer Center Institutional Animal Care and Use Committee. Orthotopic nude mouse models of ovarian carcinoma (17) were used for this study as previously described.
Western blot analysis
Western blot was performed as previously described (13). Primary antibody against EphA2 was detected with horseradish peroxidase–conjugated IgG (Amersham) and developed using an enhanced chemiluminescence detection kit (Pierce). Membranes were tested for β-actin to confirm equal loading.
Ki67 and EphA2 staining were performed using formalin-fixed, paraffin-embedded tumor sections (8-μm thickness) as previously described (8). For the evaluation of cell proliferation, the proliferative indices were determined by counting the number of Ki67-positive cells out of total number of cells in five randomly selected high-power fields exclusive of necrotic areas at ×100 magnification. The data were expressed as percentage of Ki67-positive cells. For the measurement of microvessel density, the proliferative indices were determined by counting the number of CD31-positive vessels in five randomly selected high-power fields exclusive of necrotic areas at ×100 magnification. All staining was quantified by two investigators in a blinded fashion.
Inductively coupled plasma atomic emission spectroscopy analysis for silicon content
The organs were lysed, spun down, and then analyzed for silicon content using inductively coupled plasma atomic emission spectroscopy. We detected silicon at 250.69, 251.43, 251.61, and 288.158 nm and Yttrium (1 ppm) was used as an internal control for normalization. All results were expressed as percent of injected dose.
Tissue transmission electron microscope (TEM)
The sections (100 nm) were imaged in a JEOL 1200 transmission electron microscope at 60 kV with digital images collected using a 1 k × 1 k Gatan BioScan camera Model 792.
Sample size justification and statistical analysis
We planed for n = 10 mice per treatment depending on the type of experiment. For an effect size (ratio of fixed effect and residual SD) of 0.65, this sample size was sufficient to provide 80% power for a test at significance level of 0.05. As part of preliminary analysis, we validated the normality assumption and proceeded with a nonparametric test as appropriate. The Mann-Whitney test was performed to compare the tumor sizes and tumor nodule number among different treatment groups.
In vivo safety study (blood chemistry and cytokine)
Plasma samples were collected from retro-orbital sinus and further analyzed for blood chemistry [lactate dehydrogenase (LDH), blood urea nitrogen (BUN), and creatinine] and proinflammatory cytokine production. Equivalent amounts of silicic acid (degradation product of silicon particles) and saline were used as negative controls. Cytokine levels in the supernatants were determined by ELISA kits according to the manufacturer's instructions (Bio-Rad).
Assembly of multistage system loaded with neutral nanoliposomal siRNA (DOPC-siRNA)
We fabricated S1MP using electrochemical etching and photolithography as previously described (15). These methods allow for control over the size, shape, surface properties, overall porosity, and pore size of the S1MP. For this study, we used half-dome shaped S1MPs that were uniform in size with diameter of 1.6 ± 0.1 μm (Fig. 1A and C) and had straight pores in the center with average pore size of 26 nm (Fig. 1D). The size and shape for the S1MP were selected in accordance with the mathematical vector design criteria (18, 19). In particular, the S1MP design was chosen to enhance the probability of their margination and endothelial adhesion in capillary circulation. The S1MP were functionalized with an amine group to provide for a positive surface charge (8.0 mV) to enhance the charge-based interaction of negatively charged DOPC-siRNA (−2.9 mV) within the pores of the S1MP (Supplementary Fig. S1). We first examined the loading capacity of the S1MP to achieve the maximum loading of siRNA-DOPC. DOPC nanoliposomes containing Alexa555-labeled siRNA (Alexa555-siRNA-DOPC) were used for direct measurement of loading. Alexa555-siRNA-DOPC was efficiently incorporated into the S1MP in a concentration-dependent manner (Fig. 1E). Gel electrophoresis also supported siRNA-DOPC dose-dependent loading as well as the integrity of loaded siRNA (Fig. 1E). Under this loading condition, a maximum 2.0 pg of siRNA were loaded into a single S1MP (Fig. 1E). Effective loading of alexa555-siRNA-DOPC was achievable when dried and positively charged S1MP was used (Supplementary Fig. S1), suggesting that the liposomes are loaded into the porous structure by capillary action. Approximately 35% of Alexa555-siRNA-DOPC were released from the S1MP within the first 3 hours (presumably associated with release from the surface and shallow pores), followed by gradual release of the remaining amount from the S1MP over 14 days (Fig. 1F).
Effect of multistage delivery on siRNA tumor uptake and tissue distribution
To determine the duration and extent of siRNA-DOPC delivery in vivo, we first compared siRNA distribution and tumor uptake using the S1MP loaded with Alexas555-siRNA-DOPC versus Alexas555-siRNA-DOPC alone. Mice with HeyA8 orthotopic tumors (15 days after i.p. inoculation of tumor cells) were given an i.v. injection of either S1MP loaded with a single dose of Alexa555-siRNA-DOPC (5 μg siRNA) or a single dose of Alexa555-siRNA-DOPC alone (5 μg siRNA). At day 10, siRNA fluorescence was almost absent in the tumors from mice treated with Alexa555-siRNA-DOPC, whereas fluorescence remained for >10 days in the tumor from mice injected with S1MP-Alexa555-siRNA-DOPC (Supplementary Fig. S2A). Overall, a single injection of the S1MP loaded with siRNA-DOPC resulted in enhanced siRNA uptake into the tumor parenchyma by 6-fold compared with siRNA-DOPC alone. No significant difference in Alexa555-siRNA uptake into other organs such as kidney or liver was noted (Supplementary Fig. S2B and C).
In vivo delivery of siRNA-DOPC using the multistage system
Based on the sustained delivery observed in the experiments noted above, we next investigated the duration and extent of gene silencing. We focused on EphA2 (receptor tyrosine kinase in the ephrin family; ref. 20) because EphA2 is overexpressed in >70% of ovarian cancers and is associated with poor patient outcome (21). We first evaluated the immunostimulatory potential of EphA2 siRNA and/or the DOPC nanoliposomes because immunologic effects, especially with certain sequences and delivery vehicles, have been reported (22, 23). There were no biologically meaningful alterations noted in the cytokines tested (Supplementary Fig. S3; ref. 24). We then optimized the siRNA dose required for sustained gene silencing. Mice bearing SKOV3ip1 ovarian tumors were given an i.v. injection of S1MP loaded with either single-dose EphA2-siRNA-DOPC (5 μg EphA2-siRNA) or triple-dose EphA2-siRNA-DOPC (15 μg EphA2-siRNA). The mice were sacrificed (three mice per time point) and the tumors were harvested at indicated time points and assessed for EphA2 protein expression level (Fig. 2). A single administration of triple-dose S1MP-EphA2-siRNA-DOPC resulted in >80% reduction of EphA2 expression and this effect lasted for 3 weeks (Fig. 2A and B), whereas typically a single injection of EphA2-siRNA-DOPC alone silenced EphA2 expression for only up to 5 to 6 days (13). S1MP loaded with a single dose of EphA2-siRNA-DOPC failed to silence EphA2 gene expression (data not shown). Sustained gene silencing in the tumor was also supported by immunohistochemical analysis, which showed EphA2 downregulation for 28 days (Fig. 2C). This sustained in vivo gene silencing in the tumor for at least 3 to 4 weeks following a single injection is a major technical advance over frequent repetitive dosing.
Therapeutic effect of the multistage delivery of EphA2-siRNA-DOPC
Because multistage delivery of siRNA-DOPC resulted in sustained gene silencing, we next tested the antitumor activity of this delivery method. Mice were treated either twice weekly with siRNA-DOPC (5 μg EphA2-siRNA per injection, for a total administered dose of 30 μg EphA2-siRNA over 3 weeks) or a single administration with S1MP-EphA2-siRNA-DOPC (15 μg EphA2-siRNA). No abnormal behavior or weight loss was noted during the entire treatment period (Supplementary Fig. S4). Treatment with S1MP-EphA2-siRNA-DOPC in mice with SKOV3ip1 tumor significantly reduced tumor weight by 54.2% and 65.3% compared with nonsilencing control siRNA-DOPC and S1MP-nonsilencing control-siRNA-DOPC, respectively (P < 0.05; ANOVA F = 4.92). Similarly, significant tumor weight reduction was observed in the HeyA8 model treated with S1MP-EphA2-siRNA-DOPC compared with nonsilencing control DOPC (57.4%) and S1MP-nonsilencing control-siRNA-DOPC (69.3%), respectively (P < 0.01; ANOVA F = 5.89; Fig. 3A and B). These data show that a single administration of S1MP-EphA2-siRNA-DOPC led to a comparable antitumor effect to six repeated i.v. injections of EphA2-siRNA-DOPC for a total of twice the siRNA dosage administered by the multistage strategy. The number of nodules formed was also comparably reduced by both S1MP-EphA2-siRNA-DOPC and EphA2-siRNA-DOPC in the SKOV3ip1 model (Supplementary Fig. S5). Tumor-bearing mice treated with either S1MP-EphA2-siRNA-DOPC or EphA2-siRNA-DOPC alone did not develop ascites, in contrast with control mice treated with either saline, S1MP alone, nonsilencing-siRNA-DOPC, or S1MP-nonsilencing-siRNA-DOPC (Supplementary Fig. S6). We assessed the biological effect of sustained downregulation of EphA2 by determining microvessel density (CD31) and cell proliferation (Ki67). Representative sections from each treatment group are shown with mean number of vessels per field or mean percent of proliferative cells. Compared with control groups, the mean microvessel density was significantly reduced by ∼3-fold in tumors treated with both S1MP-EphA2-siRNA-DOPC and EphA2-siRNA-DOPC (overall ANOVA: **, P < 0.001; Fig. 4). Similarly, proliferation index was also significantly reduced by 20-fold when mice were treated with both S1MP-EphA2-siRNA-DOPC and EphA2-siRNA-DOPC (overall ANOVA: **, P < 0.001; Fig. 4).
Biodistribution and biodegradation of S1MP
To examine the biodistribution of S1MP, the mice were injected with Alexa555-siRNA-DOPC loaded S1MP i.v. and the major organs including liver, kidney, spleen, lung, and heart were harvested 4 hours after the injection. Silicon content analysis showed that S1MP were primarily accumulated in the liver (53%) and spleen (11% of total injected dose), and there was no to minimal S1MP accumulation observed in the kidney, lung, and heart (Fig. 5A). To provide further evidence that the S1MP allows sustained siRNA release, S1MP conjugated with FITC (green fluorescence) were loaded with Alexa555-siRNA-DOPC (red fluorescence) and i.v. injected into mice. The liver and spleen were harvested 20 days after injection for histologic evaluation. Alexa555-siRNA-DOPC remained associated with S1MP as evidenced by the yield of yellow fluorescence, but not with macrophages (pink) in the liver and spleen at 20 days after injection (Supplementary Fig. S7A and B), indicating that Alexa555-siRNA-DOPC remains intact. The S1MP were distributed throughout the liver sinusoids and the red pulp in the spleen (Fig. 5B). Histopathologic analyses of tissue sections with H&E stain showed no obvious inflammatory infiltration in these organs. In the liver, the S1MPs were distributed throughout the sinusoids and (Fig. 5B) some were taken up by Kupffer cells (Supplementary Fig. S7A). In the spleen, the S1MPs were present in the splenic cords (Fig. 5B) and some were taken up by f4/80-positive macrophages (Supplementary Fig. S7B). Transmission electron microscopic analyses of the liver and spleen sections confirmed that S1MP remained within sinusoidal spaces in the liver and red pulp in the spleen (Fig. 5C). Silicon contents in the spleen were reduced by 80% in the first 2 weeks and cleared by the 3rd week (Fig. 6A). In contrast, only 55% of S1MP was cleared from the liver in the first 2 weeks and ∼25% of the injected S1MP remained in the liver 3 weeks after injection (Fig. 6B), suggesting that S1MP degradation kinetics are different in each organ. Scanning electron microscopic images of S1MP showed enlargement of pore size at day 7 and reduction of overall size by day 14 (Fig. 6C). In some cases, bulky surface erosion was noted (data not shown). Collectively, these data suggest that the S1MP serve as a reservoir to protect siRNA-DOPC from degradation, release them over time by a mechanism that combines degradation of the carrier material, and hindered diffusion through the nanoscopic pore.
Biocompatibility of S1MP
We next tested the biocompatibility of multistage delivery system in both an acute and chronic setting in FBV/N mice following the i.v. administration of therapeutic dose of S1MP-EphA2-siRNA-DOPC (15 μg EphA2-siRNA). Blood chemistry showed that S1MPs did not cause a significant increase in any of the parameters tested (Supplementary Fig. S8A–F). Despite significant accumulation of the S1MP in the liver and spleen, plasma LDH levels from the liver and spleen remained unchanged (Supplementary Fig. S8A and D). Similarly, tissue LDH levels in the liver and spleen were not changed at both conditions tested (data not shown), indicating that accumulation of the S1MP in the liver and spleen did not cause tissue injury. Similar to blood chemistry, the values of cytokines tested were not significantly higher in the mice injected with DOPC-loaded S1MP than in the saline-injected control animals in both acute and chronic setting, although some S1MP were taken up by macrophages (Supplementary Fig. S8G and H). These data indicate that S1MP-siRNA-DOPC is not toxic to the kidney, liver, and spleen and that no significant levels of inflammatory cytokines were induced by the S1MP or its degradation products.
The key findings from this work are that a single injection of multistage delivery system comprised mesoporous silicon particles loaded with liposomal siRNA against oncogene, EphA2, resulted in a sustained gene silencing for up to at least 3 weeks in ovarian tumor, concomitant with a substantial reduction of tumor burden with no to minimum toxicity. Many oncoproteins as well as their distinct roles have been identified in the past few decades; however, many of them are “undrugable” with traditional approaches such as small-molecule inhibitors because their crystal structures are unknown. We targeted oncoprotein EphA2 (tyrosine kinase receptor in the ephrin family), which plays roles in angiogenesis (25) and cell proliferation (26), and is difficult to target with conventional approaches. EphA2 is absent in the normal tissue but is overexpressed in different types of tumor including ovarian (27), breast (28), lung (29), and melanoma (30), with strong association with poor survival, advanced-stage, or high-metastatic potential (31). Although the dual roles of EphA2 as a pro-oncogenic or antioncogenic protein have been suggested (32), a recent study revealed that EphA2 mediates cell migration and invasion in the absence of ephrin (a cognate ligand for EphA2) through Akt phosphorylation (33). It has also been reported that EphA2 overexpression is frequently accompanied by the loss of ephrin, further supporting the pro-oncogenic role of EphA2 in cancer (34). Therefore, a disruption of the biological functions of EphA2 is a highly attractive molecular-targeted therapy approach (35).
Our data shown that the multistage delivery of liposomal siRNA (single injection of 15 μg EphA2-siRNA) led to comparable antitumor effect to repeated i.v. siRNA-DOPC injections (six injections of 5 μg EphA2-siRNA each), thus halving the siRNA dosage required to achieve an equivalent antitumor effect. Although we are focusing on EphA2 in this study, this platform could allow for highly adjustable personalized molecular targeted therapies with a suitable combination of RNAi depending on the molecular signature of each tumor type with “tunable” release kinetics of siRNA to control cancer cell growth. Many efforts have been reported to deliver RNAi; viral vectors (36), chemically modified siRNA (6), and nonviral nanocarriers including cationic liposome (37) and polycation-based carriers (38) have shown effective gene silencing effects in vitro and in vivo. However, immunogenicity, toxicity, safety concern, and unfavorable pharmacokinetics remain generally unsolved problems for these delivery strategies. Traditional approaches to the improvement of pharmacokinetics include surface functionalization of nanocarrier with polyethylene glycol (PEG) to avoid reticuloendothelial system uptake (39). PEG, however, does not prevent renal excretion and degradation of nanocarriers. In addition, PEGylation accelerates the clearance of nanocarrier from the circulation when injected repeatedly (40). Thus, with the aim of providing stability to nanocarriers containing biologically active payload and of achieving sustainedgene silencing, in this study, we used mesoporous silicon particles (S1MP) as a carrier of DOPC neutral nanoliposomes. The serum half-life (t1/2) of systemically injected DOPC nanoliposomes is ∼2.7 hours.12 The combinatorial multistage delivery system we used in this study significantly improved the pharmacokinetics of the DOPC liposome and resulted in 3-week-long sustained gene silencing of EphA2 in the tumor. It is likely that S1MP protect DOPC-siRNA from degradation and renal excretion due to their entrapment within the capillary spaces within the liver and spleen (Fig. 5). Slow release is most likely attained due to the gradual degradation of S1MP with subsequent release of siRNA-DOPC that reaches to the tumor.
Porous silicon is an attractive material (41), which has been investigated for possible applications in drug delivery by loading of nanoscale payload such as protein (42), enzymes (43), drugs (41), and nanocarriers (15). The surface chemistry on the porous silicon will play a critical role in determining the loading efficacy and release kinetics based on the type of interaction of payload and porous surface (41). We used positively charged S1MP for enhanced entrapment of the negatively charged (−2.9 mV) DOPC-siRNA. The electrostatic interactions between the pore wall surface and liposomes are likely to contribute to the sustained release of the liposomes from the porous structure as the S1MP degrades.
Mesoporous silicon is biocompatible (44, 45) and has received Food and Drug Administration approval for use in brachytherapy and drug delivery from implants (BioSilicon; ref. 46). The two delivery carrier materials used in this study, mesoporous silicon and DOPC neutral liposome, are highly biodegradable, biocompatible, and combine suitably to yield time-sustained delivery with no liver and renal toxicity in both in the acute and the chronic setting, at a dose of 25 μg of mesoporous silicon (Supplementary Fig. S8). In a separate study, we showed the safe systemic administration of 250 μg of mesoporous (10-fold the dose used here) through both i.p. and i.v. routes in mice.13 The multistage delivery system used in this study did not result in the production of the proinflammatory cytokines tested, unlike other delivery system that relies on the host immunity (47). Our data indicate that the antitumor effect mediated by the S1MP loaded with DOPC-siRNA was due to the DOPC-siRNA-EphA2 mediated gene silencing of EphA2 and not due to immunostimulatory effects.
Porous silicon is known to degrade completely into orthosilicic acid over time, which is readily excreted from the body. The mechanism of sustained liposomal siRNA delivery is likely to rely on essentially two unique characteristics and tailorable characteristics of the S1MP: biodegradation and biodistribution. Biodegradation is controlled by the overall porosity and pore size of the particles (48), which in turn is exquisitely controllable by choice of material processing parameters (41). The biodistribution of the particles is controlled by their size, shape, surface, and bulk properties (49), which are also precisely controlled during the particle fabrication processes (15). In view of the different degradation kinetics in different organs, and in particular within the liver and the spleen, altering their respective accumulations will lead to different, adjustable kinetics of release of the nanoliposome-encapsulated siRNA. Possible mechanisms involved in the geometry-dependent organ sequestration of particles are capillary size, capillary architecture, hemodynamics, and endocytosis (49).
In conclusion, in this study, we showed that a single injection of multistage delivery system comprised of mesoporous silicon particles loaded with nanoliposomal siRNA against oncogene, EphA2, resulted in: (a) sustained gene silencing for up to at least 3 weeks in ovarian tumor; (b) substantial reduction of tumor burden; (c) substantial decrease of angiogenesis and cellular proliferation; (d) no production of ascites; and (e) no detected toxicity associated with the S1MP vectors, the neutral nanoliposomes, or the therapeutic siRNA. To the best of our knowledge, this is the first study to achieve these collective goals in vivo and, in particular, in two orthotopic models of ovarian cancer. These finding encourage the development of a “library” of targets and drugs that can be further tailored toward specific genetic abnormalities in cancer.
Disclosure of Potential Conflicts of Interest
Commercialization rights on the intellectual property presented in this article have been acquired by Leonardo Biosystems Inc. from the title holder, the University of Texas Health Science Center in Houston. M. Ferrari is the founding scientist of Leonardo Biosystems, and hereby discloses a financial interest in the company. The other authors disclosed no potential conflicts of interest.
We thank Matthew Landry for assistance with manuscript preparation.
Grant Support: Department of Defense (W81XWH-07-2-0101, W81XWH-09-1-0212) and NIH (R01CA128797, R33CA122864), the State of Texas's Emerging Technology Fund, National Aeronautics and Space Administration (NNJ06HE06A), the Ovarian Cancer Research Fund Program Project Development Grant, the University of Texas M.D. Anderson Cancer Center Ovarian Cancer Specialized Program of Research Excellence (P50 CA083639), the NIH (CA110793, CA109298), the Zarrow Foundation, the Betty Ann Asche Murray Distinguished Professorship, the Baylor WRHR grant (HD050128) and the GCF Molly-Cade ovarian cancer research grant (M.M.K. Shahzad), and the Alliance for NanoHealth.
The costs of publication of this article were defrayed in part by the payment of page charges. This article must therefore be hereby marked advertisement in accordance with 18 U.S.C. Section 1734 solely to indicate this fact.
Note: Supplementary data for this article are available at Cancer Research Online (http://cancerres.aacrjournals.org/).
↵13Tanaka T., Godin B., Bhavane R., Nieves R.A., Gu J., Liu X., Chiappini C., Fakhoury J. R., Amra S., Ewing A., Li Q., Ferrari M., unpublished data.
- Received October 23, 2009.
- Revision received February 9, 2010.
- Accepted February 26, 2010.
- ©2010 American Association for Cancer Research.