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A one-pot synthesis of micellar spherical nucleic acid (SNA) nanostructures using Pluronic F127 as a thermoresponsive template is reported. These novel constructs are synthesized in a chemically straightforward process that involves intercalation of the lipid tails of DNA amphiphiles (CpG motifs for TLR-9 stimulation) into the hydrophobic regions of Pluronic F127 micelles, followed by chemical cross-linking and subsequent removal of non-cross-linked structures. The dense nucleic acid shell of the resulting cross-linked micellar SNA enhances their stability in physiological media and facilitates their rapid cellular internalization, making them effective TLR-9 immunomodulatory agents. These constructs underscore the potential of SNAs in regulating immune response and address the relative lack of stability of noncovalent constructs.
Spherical nucleic acids (SNAs) have become an important platform for programmable assembly,1 biodetection,2,3 drug delivery,4,5 and nucleic acid–based therapeutics.6 Historically, SNAs have been synthesized by covalently immobilizing a dense layer of highly oriented nucleic acids onto a spherical gold nanoparticle core.7 The resulting three-dimensional polyvalent architecture of the SNA makes it a higher affinity binder for complementary ligands than the linear sequence from which it is comprised.8 The dense oligonucleotide shell of SNAs also enhances its resistance to enzymatic degradation,9 thus increasing the overall lifetime of the oligonucleotide components. In addition, by engaging cell-surface receptors,10 SNAs can actively traverse cell membranes without the need for transfection agents. As a result, SNAs have emerged as “single-entity” intracellular diagnostic tools,2,11 gene-regulating structures,6 and immunomodulatory agents12 that exhibit minimal cytotoxicity and nonspecific immunogenic responses.13
Since the aforementioned physical and biological properties of SNAs are independent of the nature of the core,8 a broad range of materials (Au,7 Ag,14 γ-Fe2O3,15 CdSe,16 Pt, Pd) have been used as templates for their syntheses.8,16 However, concerns about the potential long-term toxicity and metabolic fate of metallic nanoparticle cores17,18 have inspired a shift to the postsynthesis dissolution of the Au NP template19 or the use of organic templates such as liposomes,20 proteins,21 and block copolymer nanostructures.22,23 Arguably, an ideal SNA is one that can be rapidly made under mild conditions from biocompatible cores in size-tunable and monodisperse forms. As an amphiphilic block copolymer that is part of many FDA-approved drugs24 and can be assembled into spherical micelles at room temperature at low critical micelle concentrations (CMC), Pluronic F12725,26 ((poly(oxyethylene)-poly(oxypropylene)-poly(oxyethylene); PEO–PPO–PEO) is such an ideal SNA core material. In addition, since it has a thermoresponsive CMC, micelles made from Pluronic F127 can be easily assembled and disassembled based upon a change in temperature—as has been demonstrated for a wide range of hydrophobic cargos27,28—a property that can be extremely useful for purifying the targeted SNA architectures.25,29
Herein, we report a strategy that utilizes Pluronic F127-based micellar templates for the facile assembly of nucleic acids comprising hydrophobic lipid tails and stretches of T bases functionalized with C6-amines into sub-50 nm biocompatible SNA constructs (Scheme 1). The C6-amines can be subsequently cross-linked with PEGylated bis(sulfosuccinimidyl)suberate to increase the stability of the SNA. With this method, particles that are not fully cross-linked can be disassembled using the temperature-dependent properties of the Pluronic F127 block copolymer core. To demonstrate the versatility of this strategy, we have synthesized SNA constructs comprising 1826 and 7909 CpG DNA sequences that are known agonists for TLR9 and evaluated their structures, stabilities, and intracellular potencies with respect to TLR9 activation.30
Above their CMC of 1 wt %, Pluronic F127 block copolymers can assemble into small (~10 nm), monodisperse micelles that consist of a hydrophobic PPO core surrounded by a hydrophilic PEO shell.31 In these size ranges, Pluronic F127-derived micelles have been shown to exhibit long in vivo circulation times and can deliver encapsulated chemotherapeutics into tumor tissues, presumably via the enhanced permeation and retention (EPR) effect.32,33 For SNA assembly, we chose to synthesize micelles of 12 ± 2 nm diameter (PDI = 0.21 as measured by dynamic light scattering (DLS), ζ = −2 mV; 2 wt % dispersion of Pluronic F127) in 1× HEPES buffered saline (HBS). Surface functionalization of these micelles was readily achieved by the addition of an amphiphilic DNA (to a final concentration of ~10 μM; see Supporting Information (SI), Section S2 and Table S1), which comprises a hydrophobic lipid tail, a block of five amine-functionalized bases, and the desired nucleic acid sequence (20–25 base pairs), followed by equilibration overnight at room temperature prior to cross-linking. The hydrophobic DPPE lipid tail, attached covalently to the DNA via Cu-free click chemistry (see SI, Section S2), allows for surface immobilization of DNA onto the hydrophobic core of the micelles. In the final step, the nucleic acid strands were cross-linked at room temperature with a commercially available bis(succinimidyl)penta(ethylene glycol) (BS(PEG)5) linker. In situ analysis of the reaction mixture shows particles with an increased size (25 ± 5 nm, PDI = 0.33) and a more negative surface charge (ζ = −15 mV), suggesting successful functionalization of the micelle core with the nucleic acid strands.
Since the CMC of Pluronic F127 is temperature-sensitive, isolation of the micellar SNAs from the excess Pluronic F127 and the non-cross-linked, unbound amphiphilic nucleic acids can be accomplished by low-temperature centrifugal filtration.25 Indeed, lowering the temperature of the dispersion to 4 °C allows for the disassembly of any nonfunctionalized micelles (or those with low levels of functionalization) into individual polymer chains after cross-linking.25 These left-over Pluronic-based components, together with unincorporated DNAs, can be removed via three low-temperature cycles of membrane-filter-centrifugation/resuspension (Figure Figure11B; see also SI, Section S2), which was verified with a standard colorimetric assay (see SI, Section S3).25
The purified micellar SNAs retain many of their as-synthesized particle characteristics (26 ± 2 nm, PDI = 0.34, ζ = −15 mV), confirming that the cross-linking was effective and the purification process did not cause a significant loss in the template-assembled DNA component (~60% DNA incorporation). Imaging of the purified micellar SNAs that have been deposited on a mica surface by atomic force microscopy (AFM, Figure Figure11C–D) showed spherical nanostructures (22 ± 8 nm) that are consistent with the addition of a shell of single-stranded DNA (~8 nm in length) onto the Pluronic F127 template. As synthesized, the average surface coverage of DNA strands on the micellar SNAs is ~150 ± 50 strands/particle, as determined by a combination of UV–vis spectroscopy (to determine total oligonucleotide content) and nanoparticle tracking analysis (to calculate the number of nanoparticles based upon dynamic light scattering and their Brownian motion) (see SI, Section S4).
The cooperative melting profiles of materials assembled from complementary SNAs are diagnostic indicators of the SNA structure.8 This cooperative binding is a consequence of the dense, uniform arrangement of nucleic acids on their surfaces, which allows them to hybridize in a polyvalent fashion. Indeed, when two samples of micellar SNAs with complementary nucleic acids were combined at room temperature, visually observable aggregates were formed that exhibited a substantial increase in melting temperature (71.5 vs 55 °C for the free DNA duplex at fixed total DNA and salt concentrations, Figure Figure22B) along with a narrow melting transition (full-width at half-maximum ~2 °C; Figure Figure22B).7
The micellar SNAs exhibit remarkable stability in biological media at physiological conditions. DNA dissociation and interparticle fusion were not observed after 7 days of storage at 37 °C, as analyzed by gel electrophoresis (see SI, Figure S5). This enhanced thermal stability can be attributed to the electrostatic repulsive forces of the negatively charged DNA strands on the particle surface.20,34 This DNA corona, which is common to SNAs, is hypothesized to decrease the propensity of SNAs to be degraded by nucleases,9 and cross-linking of the nucleic acids should further enhance the serum stability and lifetime of the SNAs. This was confirmed by a fluorescence “turn-on” experiment based on an SNA comprising a DilC18 dye-encapsulated Pluronic F127 core and a blackhole quencher (BHQ)-modified DNA shell (Figure Figure33A; also see SI, Section S8). Dissociation of the lipid-tailed DNA from the dye-labeled core should result in an increase in fluorescence and provide a measure of stability (Figure Figure33B). Indeed, incubation of the DilC18-encapsulated, BHQ-modified micellar SNAs in 10% serum media shows minimal increase in fluorescence over a period of 2 h, suggesting that the structures are quite stable in serum. In contrast, incubating the non-cross-linked precursor in the same 10% serum media resulted in a significant increase in fluorescence due to the dissociation of the intercalated DNA strands from the DilC18-encapsulated Pluronic F127 core (Figure Figure33C).
As expected, the nucleic acid shell on the surface of the micellar SNAs also facilitates their rapid cellular uptake into macrophages.12 Indeed, exposing HEK-Blue mTLR9 cells to micellar SNAs comprising Cy5-labeled DNA for 4 h resulted in significant cellular uptake in comparison to free Cy5-labeled DNA (Figure Figure44A) as evaluated by confocal microscopy and flow cytometry (Figure Figure44B). Consistent with the complete biocompatibility of its design, our micellar SNAs did not exhibit any cytotoxicity (Figure Figure44C), even at higher DNA concentrations, where delivery using traditional cationic transfection agents such as Dharmafect can cause detrimental changes in cellular morphology35 and eventual cell death.20
The ability of SNAs to independently enter cells at high concentrations via endocytosis10 has made them a promising therapeutic platform.12,36 As an example, SNAs comprising immunostimulatory (IS) nucleic acids were recently shown to accumulate in endosomes at early time points, resulting in enhanced TLR9 activation, a key requirement for producing an immunostimulatory response.12 To this end, we investigated the TLR9 immunomodulatory activity of cross-linked micellar SNAs comprising 182637 and 790938 CpG motifs, known mTLR9 agonists, in HEK- and Ramos-Blue cells, respectively. As hypothesized, we observed a dose-dependent immunostimulatory response for the micellar SNAs in both cell types in contrast to the untreated and negative controls (Figure Figure44D; see also SI, Figure S8). Importantly, the cross-linked micellar SNAs perform markedly better than linear unmodified strands where no activity was observed even at total DNA concentrations that are orders of magnitude higher than that in the SNAs.
In conclusion, this work has introduced a new and promising class of cross-linked micellar SNAs that show strong potential for therapeutic development. The ease in which this novel SNA can be synthesized and purified using a thermoresponsive template, their extended stability, and their enhanced intracellular activity all point to their potential for impacting gene regulation and immune therapy applications across a wide variety of indications.
This material is based upon work supported by the Air Force Office of Scientific Research (FA9550-12-1-0141), the National Cancer Institute of the NIH (U54CA199091), and the NTU-NU Institute for NanoMedicine located at the International Institute for Nanotechnology (IIN), Northwestern University (NU), USA and the Nanyang Technological University (NTU), Singapore. B.M., S.P.N., and A.J.S acknowledge an IIN fellowship, an NDSEG fellowship, and an NSF GRF, respectively. This work made use of the MALDI-ToF equipment (purchased with support from Northwestern University and the State of Illinois) at the NU Integrated Molecular Structure Education and Research Center (IMSERC) and the NanoSight instrument (purchased with support from the IIN) at the NU Keck Biophysics Facility.
The authors declare no competing financial interest.