Significance Small interfering RNA (siRNA) has the capacity to silence traditionally undruggable targets, but in vivo delivery barriers limit clinical translation of siRNA, especially for nonhepatic targets such as solid tumors. Most delivery strategies for RNAi cancer therapies focus on synthetic nanocarriers, but their shortcomings include limited delivery to and variable distribution throughout the target site and low therapeutic indices due to nonspecific, carrier-associated toxicities. A diacyl lipid-modified siRNA can leverage albumin as an endogenous carrier, resulting in comprehensively enhanced pharmacokinetic properties that translate to greater quantity and homogeneity of tumor accumulation relative to nanocarriers. The albumin-binding siRNA conjugate strategy is synthetically simple and safe at high doses, and thus is a translatable and potentially transformative option for RNAi oncology therapies.

Abstract Clinical translation of therapies based on small interfering RNA (siRNA) is hampered by siRNA's comprehensively poor pharmacokinetic properties, which necessitate molecule modifications and complex delivery strategies. We sought an alternative approach to commonly used nanoparticle carriers by leveraging the long-lived endogenous serum protein albumin as an siRNA carrier. We synthesized siRNA conjugated to a diacyl lipid moiety (siRNA-L 2 ), which rapidly binds albumin in situ. siRNA-L 2 , in comparison with unmodified siRNA, exhibited a 5.7-fold increase in circulation half-life, an 8.6-fold increase in bioavailability, and reduced renal accumulation. Benchmarked against leading commercial siRNA nanocarrier in vivo jetPEI, siRNA-L 2 achieved 19-fold greater tumor accumulation and 46-fold increase in per-tumor-cell uptake in a mouse orthotopic model of human triple-negative breast cancer. siRNA-L 2 penetrated tumor tissue rapidly and homogeneously; 30 min after i.v. injection, siRNA-L 2 achieved uptake in 99% of tumor cells, compared with 60% for jetPEI. Remarkably, siRNA-L 2 achieved a tumor:liver accumulation ratio >40:1 vs. <3:1 for jetPEI. The improved pharmacokinetic properties of siRNA-L 2 facilitated significant tumor gene silencing for 7 d after two i.v. doses. Proof-of-concept was extended to a patient-derived xenograft model, in which jetPEI tumor accumulation was reduced fourfold relative to the same formulation in the orthotopic model. The siRNA-L 2 tumor accumulation diminished only twofold, suggesting that the superior tumor distribution of the conjugate over nanoparticles will be accentuated in clinical situations. These data reveal the immense promise of in situ albumin targeting for development of translational, carrier-free RNAi-based cancer therapies.

Harnessing the therapeutic potential of small interfering RNA (siRNA) hinges upon enhancing its pharmacokinetic properties to overcome in vivo delivery barriers. Unmodified siRNA exhibits rapid renal clearance from circulation, leading to removal through the urine (1) and allowing minimal bioavailability in target tissues. Improving delivery of siRNA via encapsulation in nanoparticulate carrier systems has been the principal strategy used by the field. Nanocarriers can improve circulation half-life, resistance to degradation, intracellular uptake, and ultimately gene silencing potency (2⇓⇓–5). However, commonly used cationic lipid/polymer formulations are complex and expensive to synthesize and can be toxic and/or immunogenic (6, 7). Additionally, their preferential uptake by clearance organs such as the liver and spleen hinders delivery to target tissues (4, 8). siRNA conjugates have emerged as an alternative to nanocarrier-mediated delivery (9⇓⇓⇓⇓–14), offering the possibility of improving siRNA pharmacokinetics without requiring a more complex delivery vehicle. Alnylam Pharmaceuticals has demonstrated high gene silencing potency of a trivalent N-Acetylgalactosamine (GalNAc) siRNA conjugate, which binds with high specificity and affinity to the asialoglycoprotein receptor on hepatocytes (15, 16). Carrier-free gene silencing has also been achieved in the liver with siRNA–cholesterol conjugates (1, 14), but the development of siRNA conjugates that efficiently deliver to nonhepatic tissues is an unmet need. Here, we developed an siRNA conjugate that leverages endogenous albumin as a chaperone. We anticipate that albumin-associated siRNA will show particular promise as a cancer therapeutic by extending the circulation time of siRNA, enabling efficient tumor tissue penetration, and leveraging the propensity of tumor cells to internalize albumin (17, 18).

The enhanced permeability and retention (EPR) effect, based upon the high vascular permeability and diminished lymphatic drainage at tumor sites, suggests a preferential tumor accumulation of particles of nanocarrier size (∼100 nm). However, the EPR phenomenon as a tumor targeting strategy has recently come under intense scrutiny due to the discrepancy observed between preclinical and clinical efficacy of nanoparticle-based cancer therapeutics (19⇓⇓–22). There is a growing appreciation that among wildly heterogeneous human cancers, the EPR effect may be only relevant in select tumor or patient subsets. In particular, the widespread “leakiness” of tumor vasculature, a characteristic of rapidly developing mouse tumor models, has likely been exaggerated in its relevance to slower-forming human lesions (23). The field of nanomedicine has responded to these realizations with efforts to enhance understanding of nanoparticle performance in animal models (24⇓⇓–27), strategies to normalize tumor vasculature (28), systematic investigations into ideal nanoparticle characteristics (24, 29), and a focus on smaller (20–30-nm-sized) nanocarriers (24, 30, 31). Despite the promise of these approaches, the diversity of human cancers necessitates equivalently diverse delivery approaches (23, 32) and opportunity for improvement remains, particularly in the area of enhancing uniformity of tumor distribution. Nanoparticles typically exhibit concentration of dose near leaky vessels but not within more avascular tumor regions (33, 34), resulting in inhomogeneous efficacy and higher potential for incomplete remission and recurrence. Smaller, long-circulating siRNA conjugates may offer an alternative that creates more homogeneous therapeutic distribution within tumors. Indeed, the apparent tissue permeability of the serum protein albumin [hydrodynamic size ∼7.2 nm (35)] is consistently more than fourfold greater than that of 100-nm liposomes in a variety of mouse models of breast cancer (36). Here, we sought to design an siRNA conjugate that “hitchhikes” on long-circulating albumin to confer siRNA molecules with an unprecedented combination of circulation persistence and high tissue penetration to enable systemic, carrier-free delivery of siRNA for oncological applications.

In situ targeting of albumin following i.v. delivery is a viable strategy because endogenous albumin is the most abundant serum protein (>40 mg/mL) and has a circulation half-life of about 20 d (37). It is also a natural carrier of and has a high affinity for poorly soluble lipids (35, 37). Albumin has been investigated extensively as a carrier and a conjugate for small molecules as well as protein therapeutics; albumin-based therapeutics like Abraxane, Levemir, and Optison have achieved clinical relevance (35, 38), demonstrating the translatability of this approach. Previous work has established the utility of interaction of high- and low-density lipoproteins with cholesterol-conjugated siRNA (14, 39⇓⇓–42), but the natural trafficking of these lipoproteins concentrates the therapy in the hepatocytes of the liver. The potential of albumin-bound siRNA has been minimally explored (42, 43). In our unique strategy, we exploit the capacity of albumin to bind fatty acids by modifying siRNA with a lipidic moiety designed for high-affinity albumin binding. Previously, this hydrophobic modification for in situ albumin targeting was used to promote delivery of CpG DNA to lymph nodes for vaccine applications (44). We pursued modification of siRNA with a lipidic albumin-targeting agent rather than alternative albumin-binding molecules like peptide domains (45) and a truncated Evans blue molecule (46) because hydrophobically modified siRNA exhibits improved resistance to nucleases and enhanced cellular internalization (10). Thus, the strategic choice of modification with an albumin-binding lipid has the potential to confer additional advantages in siRNA stability and cell membrane interactions for uptake and endosomal escape in addition to circulation persistence, tissue penetration, and biodistribution. To investigate the clinical potential of our siRNA conjugate, we examined its efficacy as a systemic RNAi cancer therapeutic by evaluating delivery and gene silencing in translationally relevant models of human triple-negative breast cancer.

Discussion Simple conjugation of a hydrophobic albumin-binding diacyl lipid moiety to siRNA is a powerful delivery strategy to improve the pharmacokinetic properties of siRNA. L 2 conjugation increases circulation half-life, cellular internalization capacity, and tumor penetration and retention of siRNA while simultaneously reducing accumulation in clearance organs. These myriad benefits lead to enhanced and prolonged in vivo gene silencing in tumors, supporting siRNA-L 2 as a potential cancer therapy that can act on currently undruggable targets. Leveraging albumin as an endogenous nanocarrier is a relatively recent but extremely promising strategy to extend the circulation persistence of therapeutics. Clinically relevant examples range from Abraxane, an albumin-based nanoparticle that encapsulates Taxol, to Levemir, a therapeutic peptide modified to associate noncovalently with endogenous albumin (35). siRNA, with its high potential medical impact but characteristically short circulation half-life, is an ideal candidate to develop with albumin as an in vivo chaperone. Inducing high-affinity binding of siRNA to albumin via modification with a lipidic moiety is a logical strategy. Previous work has shown siRNA amenable to lipid modifications, which often confer improvements in nuclease resistance and cellular internalization without impacting gene silencing (10, 14, 49, 50). Conjugation with L 2 therefore has potential benefits on enhancing molecule stability and uptake while also prompting in situ albumin binding. Notably, this binding is noncovalent and dynamic. In its physiological role as a fatty acid carrier, albumin facilitates the cellular uptake of lipids, likely through a variety of mechanisms that use receptors for both albumin and lipid domains (51, 52). Conjugation of L 2 could allow siRNA-L 2 to hijack these natural pathways. Additionally, the hydrophobic interaction of the L 2 moiety with the cellular membrane could encourage siRNA-L 2 to be internalized independent of albumin. L 2 modification as an albumin targeting approach is desirable for achieving pharmacokinetic improvements while maintaining simplicity and safety. Despite the synthetic complexity of nanoparticle systems, siRNA-L 2 possesses a circulation half-life above that of non–cross-linked polyion nanoparticles (4, 53) and nearly equivalent to that observed in a relatively intricate cross-linked micelle system using cholesterol-modified siRNA (3). Perhaps more striking is the complete lack of toxicity observed for siRNA-L 2 at doses of 10 mg/kg, which sharply contrasts with the reported toxicity and immunogenicity of nanoparticulate carriers and our direct evaluation of in vivo jetPEI (25, 54). siRNA-L 2 couples an improved circulation half-life with a lack of dose-limiting side effects, and therefore is anticipated to enable very broad therapeutic windows when developed against specific targets. Our demonstration of MCL-1 gene silencing and its link to caspase induction demonstrates the applicability of siRNA-L 2 to such therapeutic targets. Additionally, we expect that the efficacy of siRNA-L 2 could be further optimized through modifications to enhance in vivo stability and through identification of siRNA sequences with extremely potent silencing (55, 56). Another associated challenge with nanoparticle delivery systems is their preferential accumulation within clearance organs, specifically the liver and spleen (8). Accumulation of synthetic and toxic/immunogenic nanoparticle components in these organs is the typical cause of dose-limiting toxicities. However, siRNA-L 2 avoids capture in the MPS organs, which is characteristic of nanoparticles, while also exhibiting a significant reduction in the rapid renal clearance associated with unmodified siRNA delivery. This is exemplified by the tumor:liver accumulation ratio of more than 40:1 achieved by siRNA-L 2 . The disparity between in vivo jetPEI, with a ratio of less than 3:1, is pronounced. The lack of siRNA-L 2 retention in the liver is a key advantage over nanoparticulate delivery systems and will allow a greater percentage of the injected dose to be retained at its site of action in tumors. The lower tumor:liver ratio observed with in vivo jetPEI and nanoparticle systems in the literature is consistent with reported challenges in achieving efficient nanoparticle delivery to tumor sites; in a comprehensive analysis of nanoparticle delivery to solid tumors, the median injected dose delivered to the tumor site was 0.7% (47). It is notable that even in recent, advanced, and promising nanoparticle systems, including those that use modifications for “stealth” or targeting mechanisms, the ratio of tumor:liver accumulation is consistently close to or below 1:1 (3, 5, 57⇓⇓⇓⇓–62). The marked improvement of siRNA-L 2 in relative tumor accumulation supports its translational promise. There is also a significant tumor penetration benefit of siRNA-L 2 due to its small size relative to nanoparticle carriers. Whereas in vivo jetPEI displays poor penetration of tumor tissue, siRNA-L 2 distributes homogeneously throughout tumor tissue and achieves consistently high uptake in tumor cells. The capacity of siRNA-L 2 to offer superior tumor penetration is particularly significant given the highly inconsistent nature of human tumor vasculature and tissue morphology which limits consistent nanoparticle distribution (47, 63). Here, we note that the PDX mouse model is less permissive to delivery than the orthotopic model. PDX models are considered more clinically relevant, as they preserve the native tissue architecture of the primary tumor through multiple in vivo passages and consistently recapitulate histopathologic and molecular characteristics, including drug responses and metastatic potential (64). The more challenging nature of the PDX model relative to the orthotopic model [which is considered more stringent than the flank model (21)] aligns with recent discussion suggesting that the permeable nature of commonly used mouse tumor models has led to an overestimation of the EPR effect (19, 20). Whereas nanocarriers like in vivo jetPEI may achieve efficacy in highly vascularized or nonsolid tumors (20), they lack the ability to diffuse throughout the bulk of tumor architecture. Faced with a more difficult delivery challenge in the PDX model, siRNA-L 2 maintains tumor accumulation better than does in vivo jetPEI. As the majority of human solid tumors contain regions of poor vascularization and display disparity in vessel permeability (20, 21), the performance of siRNA-L 2 in the PDX model suggests applicability to a much broader range of cancers. A recognition of the limitations of the EPR effect and a developing understanding of tumor heterogeneity calls for innovative solutions for systemic RNAi cancer therapies. siRNA-L 2 deviates enormously from the standard nanoparticle format, and its notable advantages should inspire further research into similar conjugate-based strategies. In situ targeting of albumin as an endogenous carrier is a powerful strategy to enhance the bioavailability of siRNA and avoid the issues associated with synthetic nanocarriers. siRNA-L 2 surpasses conventional delivery systems in circulation persistence, safety, biodistribution profile, tumor penetration, and cellular internalization. Ultimately, siRNA-L 2 achieves sustained gene silencing in tumors in vivo, providing strong proof-of-concept for therapeutic efficacy. This work highlights the immense value of the siRNA-L 2 conjugate as a translational and potentially transformative approach to improve i.v. RNAi cancer therapies.

Materials and Methods Materials. Amine-modified single-stranded DNA (modification at 5′ end) or RNA (modification at 3′ end) and complementary single-stranded Cy5-, unmodified DNA, or unmodified RNA was obtained from Integrated DNA Technologies (for DNA) or GE Dharmacon. The pGreenFire1-CMV plasmid was obtained from System Biosciences, and packaging plasmids pMDLg/pRRE, pRSV-Rev, and pMD2.G were purchased from Addgene. In vivo jetPEI was purchased from VWR International. The product 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[azido(polyethylene glycol)-2000] (DSPE-PEG 2000 -azide) was purchased from Avanti Polar Lipids. NucBlue Fixed Cell ReadyProbes were purchased from Life Technologies. NAP-25 filtration columns were purchased from Fisher Scientific. RNeasy Mini Kit was purchased from Qiagen, iScript cDNA Synthesis Kit from BioRad Laboratories, and Caspase-Glo 3/7 Assay from Promega Corporation. All other reagents were purchased from Sigma-Aldrich. Oligonucleotide-L 2 Synthesis. Single-stranded amine-modified oligo was reacted with 10-fold molar excess of dibenzocyclooctyne-PEG 4 -N-hydroxysuccinimidyl ester (DBCO-PEG 4- NHS) predissolved at 25 mM in DMSO. The reaction was carried out for 18 h at room temperature at a 1 mM oligonucleotide concentration in 30% DMSO and 70% PBS with 8 mM triethylamine. The product was diluted threefold in water and filtered twice through NAP-25 columns, lyophilized, and then reacted with fivefold molar excess of DSPE-PEG 2000 -azide for 24 h at a 0.1 mM oligonucleotide concentration in 50% methanol, 50% water. The reaction was diluted and filtered one time through a NAP-25 column and then purified with reversed-phase HPLC using a Clarity Oligo-RP column (Phenomenex) under a linear gradient from 95% water (50 mM triethylammonium acetate), 5% methanol to 100% methanol. The conjugate molecular weight was confirmed using MALDI-TOF mass spectrometry (Voyager-DE STR Workstation) using 50 mg/mL 3-hydroxypicolinic acid in 50% water, 50% acetonitrile with 5 mg/mL ammonium citrate as a matrix. The yield of the oligo-L 2 was quantified based on absorbance at 260 nm. The purified oligo-L 2 was annealed to its complementary strand to generate Cy5-modified, unmodified DNA-L 2 , or siRNA-L 2 . Conjugation and annealing was also confirmed via agarose gel electrophoresis. DNA was used as a cost-effective analog for siRNA in imaging studies, and is referred to as siRNA/siRNA-L 2 in the main text and SI Appendix for simplicity and cohesion (except where the figure is intended to show a direct comparison between DNA and siRNA). DNA/siRNA and DNA-L 2 /siRNA-L 2 exhibited degradation on similar time scales (SI Appendix, Fig. S3 C and D) and DNA-L 2 exhibits similar albumin binding (SI Appendix, Fig. S2B), validating its use as a model for siRNA-L 2 . Oligonucleotide-L 2 characterization. Critical micelle concentration (CMC) of oligo-L 2 was assessed fluorescently using Nile red, as described previously (65, 66). Briefly, different dilutions were prepared from a 1 mg/mL stock solution to obtain micelle samples ranging in concentration from 0.0001 to 1 mg/mL Then, 10 μL of a 1 mg/mL Nile red stock solution in methanol was added to 1 mL of each sample and incubated overnight in the dark at room temperature. The next day, samples were filtered with a 0.45-μm syringe filter, and Nile red fluorescence was measured in 96-well plates using a microplate reader (Tecan Infinite 500, Tecan Group Ltd.) at an excitation wavelength of 535 ± 20 nm and an emission wavelength of 612 ± 25 nm. The CMC was defined, as previously described (67), as the intersection point on the plot of the Nile red fluorescence versus the copolymer concentration. Degradation of siRNA and siRNA-L 2 was assessed by incubation in 60% FBS for 4 h, 2 h, 1 h, 30 min, or 15 min and evaluation by agarose gel electrophoresis with comparison with a control sample in water. Evaluation of albumin binding to oligo-L 2 in vitro. PAGE gel migration assay was used to assess binding of oligo-L 2 to BSA. Mini-Protean TGX Precast Gels of 4–20% were run in the Tetra Blotting Module (BioRad). siRNA, siRNA-L 2 , DNA, and DNA-L 2 were incubated with varying amounts of BSA for 15 min. PAGE gels were stained using GelRed Nucleic Acid Stain (Biotium) according to manufacturer protocol and imaged under UV light for visualization of nucleic acid migration. Gels were subsequently stained with Coomassie blue to evaluate BSA migration. PAGE gel migration assay was used to assess binding of oligo-L 2 to albumin in serum. siRNA or siRNA-L 2 was incubated with 9- or 13-fold molar excess BSA or 50% or 75% FBS (for approximate matching of mass of protein loaded per well). siRNA and siRNA-L 2 were imaged under UV light after poststaining with GelRed. Serum proteins were stained with Coomassie blue. Isothermal calorimetry (ITC) experiments were performed using a TA Instruments Nano ITC. Oligo-L 2 was prepared at a concentration of 0.1 mM and BSA was dissolved at a concentration of 0.25 mM from lyophilized powder in PBS. Titration experiments were carried out at 37 °C with a 300-s initial delay, 150-rpm stirring speed, and a sample cell volume (containing DNA-L 2 ) of 300 µL. Each injection was 2 µL, with an injection interval of 180 s. Data were analyzed using an independent binding site model with a blank constant correction incorporated to account for heat of dilution. All data analysis was performed in Nano ITC software. Cell Culture. Human epithelial breast cancer cells (MDA-MB-231) were cultured in DMEM (Gibco Cell Culture) supplemented with 10% FBS (Gibco) and 0.1% gentamicin (Gibco). Luciferase-expressing MDA-MB-231s were generated as previously described (5). In Vitro Gene Silencing. MDA-MB-231 cells were treated with siRNA or siRNA-L 2 complexed with in vivo jetPEI according to the manufacturer’s protocol. The siRNA was either designed against the luciferase gene (luc siRNA) or was a scrambled sequence (scr siRNA). Cells were seeded at 2,000 cells/well in 96-well black-walled plates and allowed to adhere overnight. Cells were then treated in 10% serum for 24 h at a dose of 100 or 50 nM siRNA. After 24 h, media was replaced with luciferin-containing media (150 μg/mL) before imaging with an IVIS Lumina III imaging system at 24 and 48 h. To evaluate silencing of a therapeutically relevant gene, siRNA targeting MCL-1 was used. MCF7 cells were treated with MCL-1-targeted or a scrambled control siRNA-L 2 at 200 nM in 10% serum-containing media for 24 h. At 48 h, RNA was harvested and MCL-1 mRNA levels were evaluated using quantitative real time PCR. In parallel, caspase activity was measured at 48 h using the Caspase Glo 3/7 Assay (Promega) according to the manufacturer’s protocol. Evaluation of albumin binding to oligo-L 2 in vivo. Fluorescent (Cy-5-labeled) DNA and DNA-L 2 was injected into the tail vein of CD-1 mice (4–6-wk-old, Charles Rivers Laboratories) at 1 mg/kg. Blood was collected at 20 min postinjection, and serum was isolated. Serum from mice injected with DNA, DNA-L 2 , or saline was evaluated via PAGE gel migration assay to assess binding of oligo-L 2 to albumin in vivo. In vitro evaluation using tumor spheroids. MCF7 cells (American Type Culture Collection) were cultured in DMEM supplemented with 1% penicillin-streptomycin and 10% FBS. Three-dimensional MCF7 spheroid cultures were established as described previously (68, 69). Briefly, cells were grown to 50% confluence in 2D culture. Cells were washed twice with trypsin (0.05%, Gibco), trypsin was aspirated, and cells were incubated at 37 °C for 10–15 min. Cells were resuspended in growth medium, pipetted to generate single-cell suspensions, and counted (Bio-Rad TC20 Automated Cell Counter). Single-cell suspensions (7,500 cells per 500 μL) were seeded in eight-well chamber slides (Nunc Lab-Tek II) precoated with 10 μL growth-factor-reduced Matrigel (BD Biosciences) in growth media containing 2% growth-factor-reduced Matrigel and cultured for 5 d. The 8-well chamber slides were used for evaluation by confocal microscopy; the setup was scaled up to 12-well plates for flow cytometry and down to 96-well plates for cytotoxicity studies. To evaluate tumor spheroid penetration by confocal microscopy, on day 5, cultures were treated with 100 nM Cy5-labeled DNA, DNA-L 2 , or DNA complexed with in vivo jetPEI for 4 h in fresh growth medium. Cultures were washed once with PBS and fixed for 2 min with BD Cyotfix/Cytoperm solution (BD Biosciences). After aspirating fixative and removing the plastic chamber, cultures on slides were mounted with ProLong Gold Antifade with DAPI (Molecular Probes) and secured by coverslip. Slides were stored at 4 °C before confocal imaging. Confocal imaging was performed using the Nikon C1si+ system on a Nikon Eclipse Ti-0E inverted microscopy base. The photomultiplier tube voltage, laser power, and image display settings were set for maximal signal-to-noise ratio based on control biological samples such that negative control samples lacking label had no background fluorescence and treatment samples had no saturated pixels. Image acquisition and analysis were performed using Nikon NIS Elements AR version 4.30.01. To evaluate tumor spheroid penetration by flow cytometry, on day 5, cultures were treated as described above. Cultures were washed once with PBS and tumor cells were dissociated from Matrigel for evaluation of Cy5 fluorescence. Blood Plasma Pharmacokinetics. Fluorescent (Cy-5-labeled) DNA and DNA-L 2 were injected into the tail vein of CD-1 mice (4–6-wk-old, Charles Rivers Laboratories) at 1 mg/kg. Before injection, the mouse ear was placed on a coverslip on the Nikon C1si+ confocal microscope system. An artery within the ear was set in focus, and after injection, images of the artery were automatically collected every 2 s for 30 min. After 30 min, animals were killed. Maximum initial fluorescence of the artery was set to a time of 0 s. Artery fluorescence was evaluated by averaging pixel intensity values contained in a circular region of interest located entirely within the vessel. Data were fit to a one-phase exponential decay model (equation below) and half-life and area under the curve were determined from these fits. F l u o r e s c e n c e b l o o d = F l u o r 0 × e − k t . Biodistribution in Tumor-Bearing Mice. For the orthotopic mouse tumor model, athymic nude female mice (4–6-wk-old, Jackson Laboratory) were injected in each mammary fat pad with 1 × 106 MDA-MB-231 cells in DMEM:Matrigel (50:50). After 21 d, tumor-bearing mice were injected via the tail vein with 1 mg/kg (nucleic acid dose) of fluorescent DNA, DNA-L 2 , or DNA loaded in in vivo jetPEI. After 30 min, 24 h, and 48 h, animals were killed and the organs of interest (heart, lungs, liver, spleen, kidneys, and tumors) were excised. The fluorescence intensity in the organs was quantified on an IVIS Lumina III imaging system at excitation wavelength of 620 ± 5 nm and emission wavelength of 670 ± 5 nm (n = 3 animals, n = 6 tumors). Tumor radiance data were fit to a one-phase exponential decay model (equation below), and area under the curve was determined from these fits. R a d i a n c e t u m o r = R a d i a n c e 0 × e − k t . For the PDX mouse tumor model (70), the triple-negative line HCI-010 was transplanted into one inguinal mammary fat pad (surgically cleared of endogenous epithelium) of nonobese diabetic/severe combined immune-deficient (Jackson Laboratory) female mice of 3–4 wk of age (64). After ∼8 wk, PDX tumors were harvested, cut into 4 mm × 2-mm pieces, serially transplanted into the cleared inguinal mammary fat pads of a new cohort of NOD-SCID female mice, and grown to a volume of 300–500 mm3. Tumor-bearing mice were injected via the tail vein with 1 mg/kg (nucleic acid dose) of fluorescent DNA-L 2 or DNA loaded in in vivo jetPEI. After 24 h, animals were killed, and the organs of interest (heart, lungs, liver, spleen, kidneys, and tumors) were excised. The fluorescence intensity in the organs was quantified on an IVIS Lumina III imaging system at excitation wavelength of 620 ± 5 nm and emission wavelength of 670 ± 5 nm (n = 2 animals, n = 2 tumors). Acute Toxicity in Liver and Kidney. CD-1 mice were injected with siRNA-L 2 (10 mg/kg) or in vivo jetPEI-loaded siRNA (1, 2 mg/kg). After 24 h, blood was collected by cardiac puncture and then centrifuged at 2,000 × g for 5 min. Then, plasma was harvested and tested by the Vanderbilt Translational Pathology Shared Resource for systemic levels of ALT, AST, BUN, and creatinine. Tumor Distribution in Vivo After i.v. Injection. For the orthotopic tumor model, athymic nude female mice (4–6-wk-old, Jackson Laboratory) were injected in each mammary fat pad with 1 × 106 MDA-MB-231 cells in DMEM:Matrigel (50:50). After 21 d, tumor-bearing mice were injected via the tail vein with saline, 1 or 10 mg/kg fluorescent DNA-L 2 , or 1 mg/kg DNA-loaded in in vivo jetPEI. Tumors were excised, and cells were isolated from each tumor. A mixture of collagenase and DNase was used to dissociate cells, and ammonium-chloride-potassium lysis buffer was used to remove red blood cells. Uptake of fluorescent DNA or DNA-L 2 was evaluated by flow cytometry (n = 4 animals, n = 8 tumors). Tumor cells were identified as the cell population expressing GFP, whereas the GFP-negative cell population corresponded to native mouse cells. Target Gene Silencing After i.v. Injection. Athymic nude female mice (4–6-wk-old, Jackson Laboratory) were injected in each mammary fat pad with 1 × 106 MDA-MB-231 cells in DMEM:Matrigel (50:50). After tumors reached a size of 50 mm2, tumor-bearing mice were injected i.p. with luciferin substrate (150 mg/kg) and imaged for bioluminescence on an IVIS Lumina III imaging system 30 min postinjection. Next, the mice were injected via the tail vein with 10 mg/kg (based on siRNA dose) luc siRNA or siRNA-L 2 or scr siRNA-L 2 . Alternatively, mice were injected with 1 mg/kg in vivo jetPEI complexed with luc or scr siRNA. Mice were imaged and treated at days 0 and 1 following treatment injection and imaged for bioluminescence over time. Relative luminescence was determined by measuring the raw luminescent intensity of each tumor on each day and comparing to the initial signal at day 0 (n = 10 tumors per group). Mouse body weight was evaluated at each of these time points to investigate treatment toxicity. Statistical Methods. The treatment groups were statistically compared using a one-way ANOVA test (for nonrepeated measures of more than two groups) or a two-way ANOVA (for measures repeated at multiple time points) coupled with a Tukey means comparison test. For comparison between two groups, an independent two-tailed t test was used. A P value <0.05 was deemed representative of a significant difference between groups. For all data shown, the arithmetic mean and SE are reported, and the sample size (n) is indicated. Ethics Statement. The animal studies were conducted with adherence to the Guide for the Care and Use of Laboratory Animals (71). All experiments with animals were approved by Vanderbilt University’s Institutional Animal Care and Use Committee.

Acknowledgments We thank Dr. Lauren Jackson and her laboratory for use of the Nano ITC, and Dr. Fang Yu, Prarthana Patil, Isom Kelly, Madison Hattaway, and Elizabeth Curvino for their assistance with experiments. We are grateful to the NIH (NIH NIBIB R01EB019409) and the National Science Foundation (NSF CAREER BMAT 1349604) for financial support. This material is based upon work supported by the NSF Graduate Research Fellowship Program under Grants 1445191, 1445197, and 0909667.