Carbon Nanotubes Enhance CpG Uptake and Potentiate Antiglioma Immunity

Similar to other cancers, malignant gliomas, the most common and fatal primary brain neoplasm, have developed mechanisms to evade multiple effector arms of the immune system (1). One strategy to overcome this local immunosuppressive tumor microenvironment is through the activation of the innate immune system (2–4). Toll-like receptor (TLR)-family members are pattern-recognition receptors that collectively recognize lipid, carbohydrate, peptide, and nucleic-acid structures that are broadly expressed by microorganisms. Among their key functions, TLRs enhance the uptake of microorganisms by phagocytic cells and mediate leukocyte recruitment to infected tissues (5). This broad immune activation has made TLR agonists attractive candidates for vaccine adjuvants for cancer therapy. TLRs are also expressed by brain microglia (MG) and macrophages (MP; ref. 6), and direct intracranial (i.c.) injections of high doses of CpG oligonucleotides (CpG), a TLR9 ligand, can trigger tumor rejection and induces long-term immunity against glioma and neuroblastomas in mice (7). CpG as a single intratumoral (i.t.) injection has also been studied in patients with recurrent gliomas with tolerable toxicity and partial tumor response in a few patients (2, 8). Although higher CpG doses may improve clinical efficacy, significant inflammatory response in an already edematous brain may hinder this approach. Because TLR9 is located intracellularly, we hypothesized that methods which enhance CpG internalization by antigen-presenting cells may also potentiate its immunopotency. To examine this, carbon nanotubes (CNT) were used as CpG carriers in gliomas.

CNTs are molecular-scale tubes of graphite carbon with unique mechanical properties that can be exploited for biomedical applications such as drug delivery (9). Although issues regarding the toxicity of CNT materials have been raised, recent studies (including ours) have reported that soluble functionalized CNTs (fCNT) are nontoxic (10–12). Biodistribution studies in mice have shown CNT accumulation in liver and kidneys (and no uptake by the brain) with most of the CNTs eliminated within 24 hours of intravenous (i.v.) injections (13–15). CNT uptake in tumor models has also been studied showing CNT size and preparation technique to be important in enhancing its uptake in systemic tumor models (13, 16, 17). We recently showed that fCNTs can be taken up by gliomas both in vitro and in vivo (12, 18) Compared with glioma cells, tumor-associated macrophages (TAM) were far more efficient in CNT uptake as nearly half of these cells phagocytosed CNTs after a single i.t. injection (12). Furthermore, CNS injections of CNTs in normal and tumor-bearing mice were well tolerated, only eliciting a transient and self-limiting local inflammatory response (12). Overall, these studies indicated that CNTs may be suitable carriers for macromolecule, and potentially CpG, into TAMs.

Here, we demonstrate that fCNTs enhanced CpG uptake by tumor-associated phagocytic cells and resulted in their activation both in vitro and in vivo. Furthermore, in contrast to blank CNTs or free CpG, which had no antitumor effect, a single injection of low-dose CNT–CpG complexes eradicated i.c. gliomas through activation of NK and CD8 cells. These findings demonstrate that fCNTs can improve CpG uptake into tumor-associated inflammatory cells, leading to a more robust antitumor response without inducing toxicity.

Thiolated CpG (sCpG: 5′-TGACTGTAACGTTCGAGATGA-3′) and thiolated control oligodeoxynucleotides (sODN: 5′- TGACTGTAAGGTTAGAGATGA-3′) were constructed as described by Rosi and colleagues (19) and labeled with Cy5.5 (Lumiprobe, LLC). Anti-NK1.1 (clone PK136) was purchased from eBioscience (eBioscience Inc.). Anti-CD8 Ab (clone H35) was purified as previously described (20). Control normal mouse IgG was purchased from Santa Cruz Biotechnology. Flow antibodies (Abs) to mouse NK1.1 (clone PK136), CD11b (clone M1/70), CD45 (clone 30-F11), CD11c (clone N418), CD8 (clone 53-6.7), and isotype controls were purchased from BD Biosciences or eBiosciences.

eGFP and luciferase-expressing GL261 glioma cell lines (GL261.gfp and GL261.luc) were generated as described before (21, 22). Primary bone marrow–derived monocytes (BMM) were harvested from normal C57BL/6 or CX3CR1^GFP mice. After washing the bone marrow with cold PBS, cells were isolated and collected with Cell Strainer (BD Biosciences). The isolated BMM were then cultured in L929-conditioned DMEM medium. Red blood cells and other nonadherent cells were removed by changing the culture medium in 24 hours. Cultures with more than 90% CD11b⁺ purity (as assessed by FACS) were used for experiments.

CNTs measuring 200 to 400 nm in length were generated and characterized by electron microscopy as described before (18, 23). CNT funtionalization was performed using methods described by Liu and colleagues (24). Briefly, hipco CNTs were sonicated extensively (1 hour) in a solution of 1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[amino-(polyethylene glycol) 2000] (PEG; Avanti Polar Lipids). The supernatant solution of PEG-CNT was collected after centrifugation at 24,000 × g for 6 hours. After removal of excess PEG molecules by Amicon centrifugal filter device (100 kDa), functionalized PEG-CNTs were conjugated with Sulfo-LC-SPDP (Thermo Fisher Scientific Inc.) for 1 hour at room temperature. After removal of excess Sulfo-LC-SPDP by Amicon centrifugal filter device (100 kDa; Millipore), the CNT conjugates were quantified by SpectraMax M2 spectrometer with a weight extinction coefficient of 0.0465 l mg⁻¹ cm⁻¹ at 808 nm. CNTs were then conjugated with sCpG or sODN through a cleavable disulfide bond at 4°C for 24 hours. Free sCpG was then separated from solution by Amicon centrifugal filter device (100 kDa; Millipore) and measured with NanoDrop 1000 Spectrophotometer (Thermo Scientific). CNT-bound sCpG was quantified by subtracting the unbound sCpG from total sCpG added prior to the conjugation reaction.

BMM (5 × 10⁴ cells per well in 24-well plates) were incubated with sCpG (5 μg per well), CNT–sCpG (CNT 2.5 μg–sCpG 5 μg per well), blank CNT (2.5 μg per well), or CNT–sCPG mixture. At various times, cells were collected and total RNA was isolated using the Trizol system (Invitrogen) followed by double DNase treatment and column purification using the Qiagen RNeasy Clean-up Protocol. Real-time PCR was performed in a TaqMan 5700 Sequence Detection System (Applied Biosystems) as described previously (25). PCR conditions were optimized such that a minimum of 10,000-fold range could be detected for each primer. Glyceraldehyde 3-phosphate dehydrogenase (GAPDH): 5′-GTTAGTGGGGTCTCGCTCTG-3′, 5′-GGCAAATTCAACGGCACA-3′; TNF-α: CAGACCCTCACACTCAGATCATCT, CCTCCACTTGGTGGTTTGCTA; IL-12 5′-AGAGGTGGACTGGACTCCCG-3′, 5′-AGTCTCGCCTCCTTTGTGGc-3′. IL-1β: 5′-AGGGCTGTCTGGAGTCCTC-3′, 5′-GACCAGCCGCCGCCGCAGG-3′.

After each PCR time-point, supernatant from each sample was collected and analyzed for 20 cytokines using mouse Cytokine twenty-Plex Antibody Bead Kit (Invitrogen) per manufacturer's protocol. Assay plates were analyzed by a Bioplex HTF Luminex reader (Bio-Rad Laboratories, Inc.). Cytokine concentrations were calculated using Bio-Plex Manager 3.1 software with a 5 parameter curve-tting algorithm applied for standard curve calculations for duplicate samples. Data from detectable cytokines and chemokines were compared between each group.

All animals were housed and handled in accordance to the guidelines of City of Hope Institutional Animal Care and Use Committee (IACUC). Intracranial tumor implantation was performed as described previously (25). GL261.luc or GL261.gfp cells were harvested by trypsinization, counted, and resuspended in PBS. Female C57BL/6 or CX3CR1^GFP mice that express eGFP under control of the endogenous Cx3cr1 locus (Jackson Laboratory) weighing 15 to 25 g were anesthetized by intraperitoneal (i.p.) administration of ketamine (132 mg/kg) and xylazine (8.8 mg/kg), and immobilized in a stereotactic head frame. Through a small burr hole, 3 μL of PBS containing 1 × 10⁵ tumor cells was injected unilaterally as described before (25).

Four days after i.c. tumor implantation, mice received 1 i.t. injection of PBS (control, 10 μL), free sCpG (5 μg/10 μL PBS), blank CNT (2.5 μg) mixed with free sCpG (CNT + sCpG; 5 μg sCpG/10 μL PBS), or sCpG conjugated to CNT (CNT–sCpG; 2.5 μg CNT/5 μg sCpG/10 μL PBS) through the initial burr hole. Tumor growth was assessed by Xenogen IVIS In Vivo Imaging System (Xenogen) as previously described (21).

NK and CD8 depletion studies were carried out as described (21). In these experiments mice were injected with anti-CD8, anti-NK1.1, or control IgG (200 μg per mouse, i.p.) mAb 1 day prior to tumor implantation and each i.t. injection. Leukocyte depletion was confirmed with FACS analysis of peripheral blood (21). For tumor rechallenge experiments, naive or GL261-bearing mice that had survived for at least 3 months after the initial CNT–sCpG treatment and were tumor-free by imaging, were rechallenged with i.c. GL261 (1 × 10⁵ cells).

Tumor-bearing wild-type (wt) or CX3CR1^GFP mice were injected with CNT bound to Cy5.5-labeled sCpG (CNT–sCpG^5.5, 2.5 μg CNT/5 μg sCpG/10 μL PBS) or free sCpG^5.5 (5 μg sCpG/10 μL PBS). Tumors were harvested at various time intervals and evaluated by flow cytometry as described below. For imaging, frozen brain sections were embedded in O.C.T. (Tissue-Tek) and 10-μm sections were cut using cryostat (Leica Microsystem Inc.). Sections were mounted in Vectashield mounting medium containing 4060-diamidino-2- phenylindole (DAPI; Vector). Images were obtained by AX-70 fluorescent microscopy (Leica Microsystems Inc.) and were prepared by Zeiss LSM Image Browser software.

Tumors and blood samples were harvested and examined by flow cytometry as described previously (21). Cell suspensions from brain tissue were forced through a 40-μm filter. Blood samples were incubated in Gey's buffer (pH 7.2) for 10 minutes. Freshly prepared samples were resuspended in 0.1 mol/L PBS containing 1% FBS and 2 mmol/L EDTA and incubated with FcγIII/IIR-specific Ab to block nonspecific binding. Samples were then stained with different combinations Abs or isotype controls for 1 hour at 4°C and analyzed by a CyAn fluorescence cell sorter (BDIS). Inflammatory cells were gated and separated from the rest of sorted cells base on forward vs. side-scatter analysis and their staining characteristics. FlowJo 8.4.7 software (Tree Star, Inc.) was used for data analysis and the proportion of each cell type was measured as percent of total inflammatory cells. Glioma MPs were gated as CD11b⁺/CD45^high and MG as CD11b⁺/CD45^low on the basis of previously described phenotype characterization (26).

Statistical comparison in all different experimental conditions was performed with the prism software using 2-way ANOVA or Student's t test. Survival was plotted using a Kaplan–Meir survival curve and statistical significance was determined by the log-rank (Mantel–Cox) test. A P value of less than 0.05 was considered significant.

We first evaluated in vitro loading capacity of PEG₂₀₀₀-functionalized CNTs by conjugating them with sCpG. CNT conjugation capacity plateaued at 1 to 2 μg sCpG per μg CNT, which was consistent with other oligonucleotides (24). To evaluate sCpG uptake in vitro, BMM derived from wt or CX3CR1^GFP mice were incubated with CNT bound to Cy5.5-labeled sCpG (CNT–sCpG^5.5) or free sCpG^5.5. sCpG^5.5 uptake, which mostly localized to cytoplasmic compartments, was enhanced by CNTs (Fig. 1A and B) without inducing any additional toxicity in BMM or GL261 gliomas (Supplementary Fig. S1). CNTs also increased sCpG uptake by GL261 gliomas, but not as strongly as BMM (Fig. 1C and D). These findings confirmed our hypothesis that intracellular CpG delivery can be enhanced with CNTs. Whether more efficient CpG uptake augmented monocyte activation was examined next.

CNT–sCpG was incubated with BMM and cytokine expression evaluated by qRT-PCR (quantitative RT-PCR) and ELISA. The thiolation process that was employed to link CpG with CNT appeared to suppress CpG proinflammatory function (Supplementary Fig. S2). Nevertheless, when equivalent doses of sCpG were delivered with CNT, a significant upregulation of IL-12 and TNF-α expression was seen (Fig. 2). CNT–sCpG also enhanced release of chemokines, but not VEGF, by BMM (Fig. 2). Thus, CNT appeared to not only improve CpG uptake, but also enhanced its proinflammatory function in BMM. We next tested the efficacy of CNTs as a potential CpG carrier and immunotherapy agent in i.c. gliomas.

To evaluate CNT–sCpG uptake in vivo, 2 different i.c. GL261 glioma models were used. To assess uptake by tumor-associated inflammatory cells, GL261 cells were implanted into CX3CR1^GFP mice. Although in these transgenic mice eGFP is expressed in MG, MPs, and other myeloid-derived cells, our flow cytometry studies (not shown) have indicated that the majority (more than 70%) of eGFP-expressing cells in this glioma model are MPs (CD11b⁺, CD45^high) and MG (CD11b⁺, CD45^low), based on previously-described phenotype characterization (26). In the second model, GL261.egfp cells were i.c. implanted into wt mice to measure sCpG uptake by tumor cells. Four (GL261 model) or 10 days (slower-growing GL261.egfp model) after i.c. tumor implantation, tumors were injected with CNT–sCpG or sCpG, and tumor GFP⁺ cells were sorted and examined for Cy5.5 uptake at various time points (Fig. 3A and B). Consistent with the in vitro experiments, CNTs enhanced sCpG uptake by tumor-associated inflammatory cells, and to a lesser (nonsignificant) degree, by gliomas. Interestingly, sCpG clearance was slower in CNT–sCpG^5.5-injected mice as both sCpG^5.5 particles and sCpG^5.5+ MG/MP persisted in the brains of these animals for more than 7 days after the initial injection (Fig. 3A and C). This suggested that either clearance of CNT–sCpG by inflammatory cells was slower than free sCpG or robust chemokine release in CNT–sCpG group prevented migration of sCpG^5.5+ inflammatory cells away from injection site. To further evaluate CNT–sCpG⁺ cell types, i.c. GL261 tumors in wt mice were injected with PBS (control), CNT–sCpG^5.5, free sCpG^5.5, or CNT–sCpG^5.5 mixture, and phenotypes of Cy5.5⁺ inflammatory cells characterized by FACS. As expected, CNT promoted CpG uptake by MG/MP, NK, and Dendritic cells (DC) (but not CD8 cells, not shown; Fig. 4A and B). Although 20% to 30% of tumor leukocytes internalized CNT–sCpG^5.5 particles within 2 days, the actual proportion of cells that were sCpG^5.5+ locally was probably much higher because cells from the entire tumor (and not just the injection site) were analyzed in these experiments. Also, to assess which cell types were the prominent carriers of CNT–sCpG, and to check if the decline in sCpG^5.5+ cells in the CNT–sCpG^5.5 group at 4 days was due to the migration of these cells away from the injection site or trafficking of circulating sCpG^5.5-negative cells into the tumor, we measured the total number of each cell type for all treatment groups. Neither sCpG nor sCpG–CNT treatments induced a significant change in tumor leukocyte infiltration (not shown). However, in the CNT–sCpG-treated mice, total and Cy5.5⁺ cells rapidly increased within 2 days of injection before stabilizing. Furthermore, CD11b⁺ cells (i.e., MG and MP) were the most frequent inflammatory cell and CNT–sCpG⁺ cell type within tumors. These findings suggested that (i) CNT delivery enhanced CpG-induced innate immune response to gliomas and (ii) the decline in the proportion of CpG^5.5+ inflammatory cells was most likely due to both influx of circulating cells into tumors and migration of CNT–sCpG-carrying cells out of the tumor environment. Whether this inflammatory response resulted in tumor rejection was evaluated next.

To evaluate CNT–sCpG immunotherapy, mice bearing 4-day-old i.c. GL261.luc gliomas were given a single i.t. injection of PBS (control), free sCpG, blank CNT mixed with free sCpG, or sCpG conjugated to CNT. The CNT–sCpG dose combination was selected on the basis of the CNT conjugation capacity of sCpG (discussed previously) and our recent observation indicating CpG to effectively eradicate gliomas at this dose (i.e. 5 μg), albeit after multiple injections (21). As seen in previous in vivo studies (21), a single low-dose injection of free CpG had no antitumor effect (Fig. 5A and B). In contrast, CNT–sCpG not only delayed tumor growth, but also cured 50% to 60% of mice with established gliomas. Blank CNT by itself, or CNT conjugated with control oligodeoxynucleotide (CNT–sODN), had no effect on tumor growth (Supplementary Fig. S3). The exact mechanism for this improved sCpG therapy with CNT delivery is unclear but may have been due to (i) higher sCpG uptake by tumor-associated TLR9⁺ inflammatory cells, such as MG/MP, (ii) slower intra- or extra-cellular sCpG release and clearance by CNTs (depot effect), and/or (iii) migration of CNT-carrying tumor inflammatory cells into lymphoid organs where other immune cells are activated.

To investigate inflammatory cellular responses to CNT–sCpG therapy, mice bearing 4-day-old i.c. tumors were treated with PBS, sCpG, CNT–sCpG, and CpG–sODN and local and systemic inflammatory changes analyzed by FACS (Supplementary Fig. S4). Although all agents increased CNS MG/MP, CD8, and NK cell responses, only CNT–sCpG caused a significantly higher infiltration of MG/MP over free sCpG. Furthermore, only CNT–sCpG-treated mice demonstrated a sustained elevation of circulating NK cells. These observations suggested that both MG/MP and NK cells may have played a role in CNT–sCpG antitumor response. To better characterize which cell types were responsible for tumor rejection, leukocyte depletion studies were performed next.

To verify if the antiglioma effect of CNT–sCpG was solely due to activated NK cells (as suggested by an increase in circulating NK cells), depleting doses of CD8 or NK-specific Abs were given 1 day prior to both tumor implantation and CNT–sCpG treatment. The CNT–sCpG antitumor effect was completely abrogated by either NK or CD8 depletion (Fig. 6A), indicating that both cell types played a role in tumor rejection.

Finally, to determine whether CNT–sCpG treatment induced immunity against gliomas, CNT–sCpG-treated GL261-bearing mice that had survived for at least 3 months, along with naive mice, were rechallenged with an i.c. injection of GL261 glioma. These “cured” mice developed full immunity against GL261 rechallenge (Fig. 6B).

As potent stimulators of both innate and adaptive immune systems, CpG oligonucleotides (ODN) are currently being examined for cancer immunotherapy (5). Antitumor function of CpG has also been studied in brain tumors. Although initial reports by Carpentier and colleagues demonstrated an 88% cure rate and long-term immunity in rats with i.c. gliomas (27, 28), others have shown variable CpG antiglioma responses ranging from no efficacy (29), partial response (4), and complete tumor eradication (30). One explanation for these contrasting reports may be differences in animal models and CpG constructs. Nevertheless, results from early-stage human clinical trials utilizing convection-enhanced CpG therapy in patients with recurrent malignant gliomas have been disappointing with only modest antitumor response in a few patients (2, 8). Although increasing the CpG dose may further enhance its proinflammatory effect, high i.c. CpG could exacerbate brain edema and result in CNS toxicity by activating TLR9-independent pathways (31). Alternatively, proinflammatory CpG response can be augmented with repeated injections of low-dose CpG or nanoparticles delivery systems (21, 32). Both lipid- and nonlipid-based nanoparticles have been shown to promote CpG uptake into TLR9-rich endosomes to enhance its immunostimulatory activity in vitro and in vivo (32–37). Here we demonstrate that functionalized CNTs may also be used to enhance CpG uptake by tumor-associated phagocytic cells as an immunotherapy approach. Although the use of CNTs for CpG delivery has been examined in vitro before (9, 38, 39), this is the first report demonstrating the antitumor efficacy of CNT–CpG complexes in vivo. Our data indicate that improved delivery of CpG into endosomes by CNTs and “slow-clearance” of CNT–sCpG complexes in the CNS both played a role in augmenting CpG immunotherapy in this model.

Located in the endosomal compartment, TLR9 was initially shown to specifically respond to unmethylated CpG motifs, such as those present in bacterial DNA. As a result, synthetic CpGs were designed to contain repeat unmethylated CpG motifs to enhance TLR9 engagement and phosphorothioate linkages to prevent breakdown (40). Recent work, however, suggests that DNA recognition by TLR9 depends on the 2′deoxyribose phosphate backbone and that neither phosphorothioate linkage nor specific sequences (i.e., CpG motifs) are necessary to induce the immune response (41, 42). These findings have challenged the dogma that unmethylated CpG motifs constitute the “foreign signature” that triggers TLR9. Instead, phosphorothioate linkages and CpG motifs appear to increase CpG stability, aggregation, and uptake into cells. Thus, any approach that stabilizes and improves CpG uptake into endosomal compartments may enhance its stimulatory functions. Accordingly, nanoparticles have been employed to augment CpG uptake and function (32–37). Lipid nanoparticles, for example, can not only improve CpG uptake and immunopotency (32) but, as demonstrated recently, are also critical in sequestering TLR9 migration from endoplasmic reticulum to the late endosomal compartment where it can interact with CpG (35). Although we did not correlate subcellular colocalization of CNT–CpG with TLR9 in this study, rapid CNT–CpG sequestration into cytoplasmic compartments seen here suggests that CNTs were responsible for augmenting CpG prostimulatory function by facilitating its uptake.

CNTs can enter cells through several mechanisms including phagocytosis, diffusion, or receptor-mediated endocytosis (43). This internalization process depends not only on the target cell type but also on a variety of CNT characteristics such as size, clustering, and surface charge. Here, we noted CNTs to enhance CpG uptake by both monocytes and gliomas in vitro. CNT uptake, however, was more efficient in phagocytic BMM and resulted in upregulation of proinflammatory cytokines/chemokines. Similarly, in i.c. tumors, CNT-mediated CpG uptake was more efficient in TAMs suggesting active phagocytosis/endocytosis of CNT–sCpG complexes by these antigen-presenting cells. In fact, MG and MP collectively accounted for the highest number of CNT–sCpG positive cells in tumors. Early increase in tumor MG/MP, followed by sustained elevation of circulating NK cells indicated that stimulation of TAMs into M1 phenotype by CNT–sCpG may have triggered induction of antiglioma NK and CD8 cells. However, as NK cells also internalized CNTs very efficiently, it is not clear if their stimulation was entirely dependent on TAM activation or due to CNT–sCpG uptake. Future studies will evaluate the differential contribution of MG/MP and NK cells to CNT–sCpG immune responses.

Another potential mechanism that may have accounted for enhanced CpG immunopotency is the unique CNT–sCpG biodistribution within the CNS. Because of the blood–brain barrier and first-pass clearance by liver and lungs, CNTs typically do not penetrate normal brain tissue after i.v. injections (13–15). Biodistribution of CNTs following i.c. injections has not been studied before. But recently, we demonstrated that fCNTs are efficiently phagocytosed by TAMs in i.c. gliomas where they can remain for nearly 1 week after direct i.t. injections (12). Similarly, CNT–sCpG complexes studied here remained within i.c. tumors longer than free CpG. Slow clearance of CNT–sCpG complexes from the CNS may have provided a “depot” effect, allowing enough time for migration of inflammatory cells into the tumor environment and inducing a stronger antiglioma effect.

Toxicity has been raised as a potential limitation of CNT biomedical application. Although CNTs can be biodegraded through enzymatic catalysis (44), pristine (nonmodified/nonfunctionalized) CNTs have been shown to persist for several months, raising concerns of potential negative health effects (45). CNT toxicity, however, is strongly related to physicochemical properties (such as structure, length, surface area, degree of metallic contamination, and surface coating) and can be minimized with functionalization techniques (11, 46). PEG-functionalized CNTs, for example, have been shown to be nontoxic, and cleared from biliary and renal pathways within 2 months of i.v. injection in mice (47). Consistent with our previous report, fCNTs studied here were nontoxic after i.c. injections in these short-term experiments, thereby supporting their utilization in cancer immunotherapy.

CNTs may have various potential advantages over other nanomaterials in biomedical applications. fCNTs can be used to deliver siRNA into “hard-to-transfect” cells such as MPs and T cells that are usually inert to conventional liposomal transfection agents (48). They can also be used as contrast agents in multimodality optical imaging and, as they do not contain heavy metals, have a safer chemical composition as compared with gold/silver-containing quantum dots (49). Finally, the high optical absorbance of CNTs can be used in photothermal therapy, which may potentially be combined with CNT-based chemotherapy and gene therapy of cancer (24, 50).

In summary, we demonstrated CNT delivery system to significantly enhance CpG immunotherapy, eradicate i.c. gliomas at low doses, and induce immunity against tumor rechallenge without inducing toxicity. Our findings have direct implications to the development of CNT-based treatments for malignant brain tumors. Considering that fCNTs can be used to carry other oligonucleotiedes such as siRNA (51), this strategy can be employed to overcome local immunosuppressive microenvironment through modulations of tumor inflammatory responses.

No potential conflicts of interest were disclosed.

The authors thank Dr. Harish Manohara (Jet Propulsion Laboratory, Pasadena, CA) for providing the carbon nanotubes, Dr. Piotr Swiderski for generating thiolated CpG constructs, Dr. Brian Armstrong for assisting with confocal microscopy, and Dr. Simon Lacey and Shu Mi (Clinical Immunobiology Correlative Studies Laboratory) for conducting the Luminex studies.

This work was supported by R21CA131765-01A2 (B. Badie), P01-CA030206 and CA077544 (D.J. Diamond), James S. McDonnell Foundation (B. Badie), and ThinkCure Foundation (to B. Badie and D.J. Diamond). The City of Hope Flow Cytometry Core was equipped in part through funding provided by ONR N00014-02-1 0958, DOD 1435-04-03GT-73134, and NSF DBI-9970143.

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.