|Home | About | Journals | Submit | Contact Us | Français|
Recent advances in RNA nanotechnology have led to the emergence of a new field and brought vitality to the area of therapeutics (Guo P, The Emerging Field of RNA Nanotechnology, Nature Nanotechnology, 2010). Due to the complementary nature of the four nucleotides and its special catalytic activity, RNA can be manipulated with simplicity characteristic of DNA, while possessing versatile structure and diverse function similar to proteins. Loops and tertiary architecture serve as mounting dovetails or wedges to eliminate external linking dowels. Unique features in transcription, termination, self-assembly, self-processing, and acid-resistance enable in vivo production of nanoparticles harboring aptamer, siRNA, ribozyme, riboswitch, or other regulators for therapy, detection, regulation, and intracellular computation. The unique property of noncanonical base-pairing and stacking enables RNA to fold into well-defined structures for constructing nanoparticles with special functionalities.
Bacteriophage phi29 DNA packaging motor is geared by a ring consisting of six packaging RNA (pRNA) molecules. pRNA is able to form a multimeric complex via the interaction of two reengineered interlocking loops. This unique feature makes it an ideal polyvalent vehicle for nanomachine fabrication, pathogen detection, and delivery of siRNA or other therapeutics. This review describes methods in using pRNA as a building block for the construction of RNA dimers, trimers and hexamers as nanoparticles in medical applications. Methods for industrial-scale production of large and stable RNA nanoparticles will be introduced. The unique favorable PK (pharmokinetics) profile with a half life (T1/2) of 5–10 hours comparing to 0.25 of conventional 2′-F siRNA, and advantageous in vivo features such as non-toxicity, non-induction of interferons or non-stimulating of cytokine response in animals will also be reviewed.
Nanotechnology involves modification, engineering, and/or assembly of organized materials at the nanometer scale[1–4]. RNA molecules can be designed and manipulated at a level of simplicity similar to DNA[5–11], while possessing the versatility in structure, function, and even enzymatic activity similar to that of proteins[5,12–18]. This property makes RNA an attractive candidate for nanotechnological applications. Building-blocks are first synthesized after computing intra- and inter-molecular folding[19–24]. Nanoparticles are then built via spontaneous templated [5,14,15] or nontemplated self-assembly as planned[6,7].
In recent years, more and more functional RNA molecules, naturally or artificially engineered, have been discovered. Like antibodies, RNA aptamers selected from systematic evolution of ligands by exponential enrichment (SELEX)[25–29] are able to bind to specific targets, including proteins, organic compounds, and nucleic acids[30–32]. The ability to recognize specific cell surface markers through the formation of binding pockets and the capability of internalization by the targeted cells pave a new way for targeted delivery[33–37]. In the early 1980s, Thomas Cech and Sydney Altman found RNA molecules had the ability to catalyze chemical reactions. In 1998, Andrew Fire and Craig Mello discovered RNAi (RNA interference), which can regulate gene expression on a post-transcriptional level. These RNA molecules have significant therapeutic potential and are capable of regulating gene function by intercepting and cleaving mRNA or the genome of RNA viruses. The discovery of RNAi has heightened interest in RNA therapeutics, since several RNA based therapeutic approaches using small interfering RNAs (siRNAs)[4,40–45], ribozymes[46–49], and anti-sense RNAs[50,51,51] have been shown to down-regulate specific gene expression in cancerous or viral-infected cells. The successful application of RNA-based therapeutics for the treatment of cancer and infectious diseases requires several features: 1) intact delivery to desired cells; 2) capability of entering cells; 3) surviving degradation by nucleases within the cell; 4) trafficking into the appropriate cell compartments; 5) correct folding of siRNA or ribozyme in the cell, if fused to a carrier; 6) specific delivery to cells; and 7) the release and incorporation of siRNA into RISC once siRNA is delivered into cells. In addition, the RNA particle should have low toxicity and high retention times in the body. Hence, the development of a safe, efficient, specific, and nonpathogenic system for the delivery of therapeutic RNA is highly desirable.
Bacterial virus phi29 DNA packaging RNA (pRNA) molecule contains an intermolecular interaction central domain and a helical domain as the 5′/3′ paired region (Fig. 1A). Via the interaction of two interlocking loops, the pRNA molecules form dimers, trimers, hexamers, and patterned superstructures. This property of forming self-assembled nanostructure makes pRNA ideal building blocks for bottom-up assembly. The pRNA interlocking central domain is a nucleation core with very low free energy, which folds independently of the newly incorporated moieties. Thus, pRNA can be engineered and fabricated as a polyvalent and nanoscale delivery system capable of delivering multiple therapeutics into specific cells. Incubation of the pRNA containing receptor-binding moieties and gene-silencing subunits, resulted in cell binding and transportation of the chimeric pRNA/siRNA, pRNA/ribozyme into cells, subsequently silencing the targeted genes and modulating programmed cell death[53–55].
pRNA can be chemically synthesized and modified starting from small RNA fragments. The resulting nanoparticle can be assembled through the bottom-up assembly approach. The structural and molecular features of phi29 pRNA allow its easy manipulation, making it possible to redesign its components as gene targeting and delivery vehicles (Fig. 1D).
All linear double-stranded DNA viruses including bacteriophage phi29 possess a common feature that their genome is packaged into a preformed procapsid during the maturation of the viron. This process is accomplished by an ATP-driven packaging motor (Fig. 1C). However, the most exciting aspect of the phi29 DNA packaging process is the discovery of a small viral RNA, called pRNA(Fig. 1A), which is 120 bases and transcribed from the left end of the phi29 genome. It has also been revealed that pRNA contains two functional domains[58,59], one facilitates the formation of pRNA hexameric ring (Fig. 1B) and binds to the connector while the other binds to the DNA-packaging enzyme gp16. By using the energy from gp16 hydrolyzing ATP, this very powerful DNA packaging motor then gears the viral genome into the preformed procapsid. After the complete packaging, it is possible that pRNA leaves the connector before the collar protein gp11 and tail knob gp9 protein block the connector channel and assemble the intact viral particles.
pRNA is a crucial component in the phi29 DNA packaging motor and contains two functional domains (Fig. 1A). The intermolecular interaction domain is located at the central region (bases 23–97) and within this domain there are two loops (right hand loop and left hand loop) which are responsible for the hand-in-hand interaction through the four complementary base sequences within these two loops. The other domain is a DNA translocation domain which is located at the 5′/3′ paired ends. The right hand loop (bases 45–48) and the left hand loop (bases 82–85) allow for the formation of pRNA dimers, trimers and hexamer rings via intermolecular base-pairing [5,62].
Nucleotides 23–97 are the key components in the formation of pRNA multimers. This pRNA interlocking central domain constitutes a nucleation core with very low free energy. As mentioned before, pRNA is constituted with two domains and both of them can fold independently. The ability to form pRNA multimers is not affected by 5′ or 3′-end truncation before residue #23 and after residue #97. Thus, end conjugation of pRNA with chemical moiety of fusing pRNA with a receptor-binding RNA aptamer, siRNA, or ribozyme would not disturb pRNA dimer formation or interfere with the function of inserted moieties [53–55,63,64].
To simplify the description of RNA construction and multimer assembly, uppercase letters will be used to represent the right hand loop of pRNA and lowercase letters to represent the left hand loop (Fig. 1A). The same letters in upper and lower cases indicate complementary sequences for loop/loop interaction, while different letters indicate non-complementary loops. For example, pRNA A–b′ represents pRNA with a non-complementary right loop A (5′G45G46A47C48) and a left loop b′ (3′U85G84C83G82). Dimer formation requires a right loop B (5′A45C46G47C48) and left loop a′ (5′C45C46U47G48) of pRNA B-a′.
Taking advantages of the folding independence of pRNA’s two functional domains, end conjugation of pRNA with chemical moiety, fusing pRNA with a receptor-binding RNA aptamer, siRNA, ribozyme or other chemical groups generally do not disturb the interlocking interaction or interfere with the function of inserted moieties (Fig. 1D). Then, the engineered monomeric pRNA chimera (Fig, 2) can be further assembled as various nanoparticles including dimers, trimers and tetramers through different strategies.
The pRNA double-stranded 5′/3′ end helical domain and intermolecular binding domain fold independently of each other. Complementary modification studies have revealed that altering the primary sequences of any nucleotide of the helical region does not affect pRNA structure and folding as long as the two strands are paired. Extensive studies revealed that siRNA was a ~21–23nt RNA duplex [41,42,45,66]. Thus, it was possible to replace the helical region in pRNA with double-stranded siRNA. A variety of chimeric pRNAs with different targets were constructed to carry siRNA connected to nt# 29 and 91 of the pRNA (Fig. 1A). Such a pRNA/siRNA chimera was proven to be the building block which successfully inhibited targeting gene expression. A pRNA/siRNA chimera harboring siRNA targeting coxsackievirus B3 (CVB3) protease gene was constructed and was able to knock down gene expression specifically and inhibit viral replication in vitro. We also selected a model involving the Metallothionein-IIA (MT-IIA) gene as a proof of concept. The specific knock-down of the MT-IIA gene by constructed chimera pRNA/siRNA (MT-IIA) can reduce ovarian cancer cells viability significantly. Pre-clinical study also showed that pRNA/siRNA chimera targeting anti-apoptotic factor survivin gene can drive cancer cells undergo apoptosis and prevent tumorigenesis in xenograft mice models[53,54].
pRNA chimera harboring ribozyme (Fig. 2). Using the circular permutation approach[69–71], almost any nucleotide of the entire pRNA can serves as either the new 5′ or 3′-end of the RNA monomer. Connecting the pRNA 5′/3′ ends with variable sequences did not disturb its folding and function[53–55,63,64]. These unique features, which help prevent two common problems: exonuclease degradation and misfolding in the cell, make pRNA an ideal vector to carry therapeutic RNA such as ribozyme. A pRNA-based vector was designed to carry hammerhead ribozymes that cleave the hepatitis B virus (HBV) polyA signal. The pRNA/ribozyme(survivin), which targeted the anti-apoptosis factor survivin to down-regulate genes involved in tumor development and progression, was also shown to suppress survivin expression and initiate apoptosis.
In vitro SELEX[31,32] of RNA aptamers which bind to specific targets has become a powerful tool for selecting RNA molecules that target specific cell surface receptor. Aptamers were linked to the 3′ and 5′ end of pRNA. To facilitate independent folding, poly U or poly A linkers were placed between the pRNA and the aptamer. The nascent 5′/3′ end of the pRNA were relocated to nt 71 and 75 (Fig. 1A) using the circular permutation approach[69,72]. The tightly folded nt 71 and 75 region protected the 5′/3′ end from exonuclease digestion. One of the pRNA/aptamer constructs harboring anti-HIV gp120 aptamer was proved to bind to and are internalized into cells expressing HIV gp120. Moreover, the pRNA-aptamer chimeras alone also provide HIV inhibitory function by blocking viral infectivity in an acute in vitro challenge assay.
Chemical ligands like folate which can recognize specific cell surface markers can also be conjugated to pRNA for specific targeting [64,67,68]. A complementary DNA oligo can be annealed to the end of the pRNA which has the 3′-end extension with 14–26 nucleotides. The assembled folate-pRNA nanoparticles are able to bind and internalize into cancer cells specifically and efficiently (Fig. 3A) and were applied for systematic target delivery of therapeutics in vivo (Fig. 3B). Synthetic DNA oligos functionalized with different chemical groups, such as folate, were used for therapeutic pRNA construction (Fig. 2). Details of the pRNA labeling strategies are discussed below (section 5.1.3).
Unlike most of the other nanodelivery system, pRNA technology offers the possibility to form multivalent nanoparticles with accurate control of the stoichiometry of the different functional elements. Detection, ligand targeting, and drug or gene delivery elements can be conjugated to pRNA and then assembled into one nanoparticle through the bottom-up approach. Although, synthetic RNA can be modified with a wide variety of reactive moieties for chemical conjugation, they will be not discussed in this paper. Readers can refer to a previous review. Alternatively, many different strategies have been developed for post-transcriptional or co-transcriptional functionalization of RNA molecules. These labeling strategies have been demonstrated to be highly efficient for long chain RNA, such as pRNA (120 bases), and can be distinguished following single molecule labeling or random labeling of the whole chain of the RNA.
Bifunctional alkylating agents are known to promote crosslinking of DNA or RNA molecules. Using a similar strategy, post-transcriptional fluorescent labeling of the pRNA molecule was readily achieved using functionalized fluorophores, harboring a mono-alkylating reactive group, developed by Mirus (Label IT labeling reagent, Mirus). More recently, it was demonstrated that T7 RNA polymerase can be used for in vitro enzymatic fluorescent labeling of the RNA molecule using the new reagent tCTP. Different T7 RNA polymerase mutants were constructed to recognize and permit the incorporation of 2′-modified triphosphate ribonucleotide such as 2′-Ome, 2′-F, 2′-NH2, 2′-N3 into the RNA chain[77–80]. Reactive functions (amino or azido) can be imagined to further conjugate to the RNA molecules. Alternatively, 2′-F pRNA molecules were constructed and shown to present an improved resistance to RNase degradation compared to unmodified RNA, when both pyrimidines were substituted by their 2′-F counterparts.
Although it is not difficult to incorporate a single label during solid phase synthesis of short RNA, synthesis of long RNAs greater than about 80 nts only rely on the enzymatic methods and the single labeling of the RNA is hard to achieve with high labeling efficiency. To overcome this challenge and label the longer RNA with a single functional group, AMP and GMP derivatives which have been demonstrated to be efficient initiators in RNA transcription by T7 RNA polymerase but cannot be used in the elongation step, were designed (Fig. 4). Efficient labeling of RNA molecules at the specific 5′ position can be readily achieved by either one-step transcription initiation or a two-step procedure of transcription and post-transcriptional modification. Various kinds of AMP and GMP derivatives were synthesized by conjugating different chemical groups with AMP or GMP through linker molecules through established chemistry[64,82–85]. The amino- and thiol- reactive derivatives, AMP-hexanediamine (HDA)[82,86] and 5′-deoxy-5′-thioguanosine-5′-monophosphorothioate (GSMP) respectively, present both reactive moieties for further conjugation with ligands or detection markers for the production of deliverable polyvalent therapeutic particles. Whereas the synthesis of GSMP requires a more complicated chemical process, an AMP-HDA derivative was synthesized in one-step through the direct coupling of HDA to AMP at pH 6.5 in the presence of 1-Ethyl-3-[3-dimethylaminopropyl]carbodiimide hydrochloride (EDC) . AMP-HDA can then be purified either simply by removing the excess of HDA using ion exchange chromatography or reverse-phase chromatography.
The reactive aliphatic amine of AMP-HDA can be used for further functionalization by common coupling reactions with N-hydroxysuccinimide (NHS) activated compounds. Fluorescent dyes (FITC, Cy5, Cy3), targeting moieties (folic acid), or also biotin can be coupled to AMP-HDA and the resulting derivatives are shown to be efficient for the construction of single labeled pRNA molecule. Alternatively, these NHS activated compounds can be directly coupled to the end NH2 group of single labeled RNA fragments as a post-transcriptional labeling approach.
Unlike most of the common dyes and biotin, folic acid is not commercially available through its NHS ester activated form. Reaction of folic acid in the presence of N,N′-dicyclohexylcarbodiimide (DCC), NHS, and triethylamine (TEA) in dimethylsulfoxide (DMSO) lead to its conversion into its NHS ester derivatives, which can be purified from the reaction mixture by precipitation. Alternatively, folate labeling of pRNA was also achieved through a two-step procedure involving primarily the coupling of the folate-NHS ester with a 5′-NH2-DNA oligo. HPLC purification of the coupling product, followed by the annealing with pRNA has led to pRNA-folate conjugates.
SH-groups, provided by GSMP, can be used to link either a NH2-group via a hetero-bifunctional crosslinker such as N-[β-Maleimidopropyloxy] succinimide ester (BMPS) or any common chemicals that contain maleimide, vinyl sulfone or pyridyl disulfide. Using similar approaches, it was possible to efficiently synthesize RNA directly and incorporate traditional coupling reactive groups, such as amino –NH2, -COOH, Maleimide, or NHS for constructing polyvalent RNA nanoparticles. The NH2- group was used to link any particles with a COOH-group with the help of EDC. NH2/NH2 interactions can be achieved via heterobifunctional crosslinkers.
One problem in RNAi therapy is the requirement for the generation of relatively large quantities of RNA. Industrial scale of chemically synthesized RNA is one of the approaches to scale up the RNA synthesis. However, each pRNA nanoparticle is over the size limit of commercial RNA synthesis (~80 nucleotides). To produce polyvalent therapeutic pRNA nanoparticles in a large scale quantity, the phi29 pRNA can be assembled from two pieces of pRNA modules. A similar principle in using two-piece modules can be applied to the assembly of therapeutic pRNA chimeras. Besides the two-piece modules reported recently, other modules from different locations and regions of the pRNA template were designed and tested.
Different kinds of two-piece modules were constructed by opening at the different positions of the pRNA. After chemical or enzymatic synthesis of each fragment, the two RNA fragments are annealed to form the intact particle, simply by mixing them together, heating up to 80°C and slowly cooling down to room temperature. The assembled two-piece pRNA modules maintain the folding characteristics of the intact pRNA and are able to form a dimer with its partner. Preliminary data also demonstrated that the chimeric pRNA two-piece modules can be processed and silence the target gene in the same manner as the intact particle.
Enzymatic ligation of the two-piece RNAs into one intact particle is found to be an efficient strategy to face the dissociation problem observed in some two-piece RNAs. Within the pRNA structure, we have already found one high-yielding ligation site in the pRNA interlocking domain. After synthesizing the small RNA fragments separately, the additional RNA ligation used to assemble the longer RNA fragments is realized using T4 RNA ligase. The ligation of the fragments will ensure the stability and the correct folding of the entire particle.
The self-assembly of pRNA nanoparticles is a prominent bottom-up approach and represents an important idea that biomolecules can be successfully integrated into nanotechnology[7,53,54,94,95]. Such an approach relies on the cooperative interaction of individual RNA molecules that spontaneously assemble in a predefined manner and form larger 2D or 3D-structures.
There are two main categories of self-assembly: non-templated and templated nanoparticle assembly. Non-templated assembly involves the formation of a larger structure by individual components without influence from external forces. The formation of pRNA dimers, trimers and tetramers falls into this category. On the contrary, template nanoparticle assembly involves the interaction of RNAs under the influence of a specific external force, structure, or spatial constraint. In the phi29 bacteriophage, pRNA dimers serve as the building blocks to form a hexameric ring through the binding to the connector embedded in the viral procapsid which serves as the template for hexameric ring assembly.
Hand-in-hand dimers are formed by the intermolecular interaction of interlocking right and left loops that are trans-complementary (Fig. 5A). For example, pRNA Ab′ molecule interacts quantitatively with an equal mole ratio of pRNA Ba′ molecule, forming a dimer in the presence of at least 5 mM Mg2+. Dimers of an extended configuration (twins) can also be efficiently self-assembled in solution by introducing a palindrome sequence (5′GCUAGC3′) into the 3′-end of the RNA chimera (Fig. 5C). The assembled foot-to-foot dimer (twin) is formed by annealing such a 3′-end overhanged sequence by simply heating up to 80°C and slowly cooling down to room temperature.
A similar mechanism is utilized to construct chimeric pRNA trimers. When molecules of pRNA Ab′, Bc′ and Ca′ are mixed together at equal mole concentrations (Fig. 5B), stable pRNA trimers are formed with very high efficiency (up to 100%) via the interlocking loops of the three pRNAs[5–7] in the presence of 5 mM Mg2+.
The use of small RNA in gene therapy was significantly hampered due to the difficulties of producing a safe and efficient system which is able to specifically recognize and target specific cells. The strength of using phi29 pRNA as a delivery vehicle relies on its ability to easily form stable multimers which could be manipulated and sequence-controlled[5,6,61]. This particular system provides unprecedented versatility in constructing polyvalent delivery vehicles by separately constructing individual pRNA subunits with various cargos and mixing them together in any desired combination.
These nanoparticles can carry multiple components, including molecules for specific cell recognition, image detection, endosome disruption, and therapeutic treatment (Fig. 6). One subunit of the deliverable RNA nanoparticles (dimer, trimer or tetramer) can be modified to carry a RNA aptamer that binds to a specific cell-surface receptor, thereby inducing receptor-mediated endocytosis. The second subunit of the multimer can carry reporting molecules such as gold particles or fluorescent beads for the evaluation of cell binding and entry. The third subunit can be re-engineered to carry components that can be used to enhance endosome disruption so that the therapeutic molecules are released. The fourth (or fifth and sixth, if needed) subunit of the RNA nanoparticles can carry therapeutic siRNA, ribozyme RNAs, antisense RNA, or other drugs to be delivered.
Phi29 pRNA-derived carriers act as an innovative and versatile targeted delivery system for cancer treatment. Therapeutic options for patients with cancer are extremely limited. A high percentage of late-stage cancers are also resistant toward current conventional chemo- or radio-therapies. Thus, there is an urgent need to develop a new treatment regime for patients suffering from cancers. Our work using pRNA as a vector to specifically deliver therapeutics to targeted tumor cells serves both as a model to prove the concept of using RNA nanotechnology for cancer treatment and will pave a way toward clinical trials for noninvasive treatment of cancer. One might ask why use phi29 pRNA nanoparticles over the numerous other anti-cancer delivery platforms under development. The phi29 pRNA system is unique and offers the following numerous advantages: 1) polyvalent delivery; 2) controllable structure and precise stoichiometry; 3) nanoscale size; 4) targeted delivery; and 5) non-induction of antibody to ensure repeated treatments.
The polyvalent pRNA nanoparticles can deliver up to six kinds of molecules to specific cells including therapeutics, detection molecules, drugs, or other functionalities. This particular system provides unprecedented versatility in constructing polyvalent delivery vehicles by separately constructing individual pRNA subunits with various cargos and mixing them together in any desired combination. For example, the deliverable pRNA nanoparticles can be re-engineered to carry therapeutic siRNAs, ribozyme RNAs, antisense RNAs against multiple targets or different regions of one target gene, and RNA aptamers or folic acid for delivery. The other subunits of the pRNA nanoparticles may carry anti-cancer drugs to enhance the therapeutic effect or to overcome the drug resistance by combination therapy. The therapeutics or detection molecules may also be combined into one nanoparticle, making the concomitant therapy and detection of the therapeutics possible with only one administration.
The homogeneity in size of the pRNA nanoparticles is of extreme importance. Highly efficient and controlled bottom-up self-assembly yields nanoparticles with well defined structures and stoichiometry. This characteristic is highly valuable for the reproducible manufacturing of drugs for increased safety and will facilitate the U.S. Food and Drug Administration (FDA) approval of the therapeutic reagents.
It is commonly accepted that the size of a nanoparticles is paramount for effective delivery to diseased tissues. Many studies suggest that particles ranging from 10–100 nm[96–98] are the optimal size for a nonviral vector: large enough to be retained by the body, yet small enough to pass through the cell membrane and access the cell surface receptors. During the development of solid tumors, angiogenesis occurs to supply enough oxygen and nutrients to the fast growing tumor cells. The angiogenic blood vessels, unlike the tight blood vessels in most normal tissues, have gaps between adjacent endothelial cells. This allows the particles that are usually excluded from the normal tissue to extravagate through these gaps into the tumor interstitial space and concentrate in the tumor, in a size-dependent manner. The pRNA nanoparticles (dimers, trimers or tetramers) have optimal sizes ranging between 20 and 40 nm which improves the biodistribution of the therapeutic pRNA nanoparticles in the blood circulation system while the average size of a normal single siRNA molecule is well below 10 nm, which represents a major challenge for the siRNA delivery in vivo. In addition, the polyanionic nature of RNA makes it difficult to penetrate the cell membrane, and non-formulated siRNAs have been reported to be easily excreted by the body[99–102]. Nanoparticle delivery of siRNA or other therapeutics has the potential to improve the PK, pharmacodynamics, and biodistribution, as well as to provide a lower toxicity in treatment, as discussed in Section 8.
Furthermore, the PK and pharmacodynamics of the pRNA nanoparticles has been improved by introducing chemical modifications to the RNA backbone. The chemically modified RNA can be resistant to RNase, which makes RNA nanoparticles more stable and increases their retention time during blood circulation. The specific delivery and longer retention time of pRNA nanoparticles also assures the usage of a lower dose for the treatment.
pRNA nanoparticles can carry both a therapeutic agent and a recognition ligand for targeted delivery to specific cells. The incorporation of a receptor binding aptamer, folate, or other ligands to the pRNA complex with simple procedures ensures the specific binding and targeted delivery to cells. In combination with the advantage of nano-scale size, the system provides the both advantages of higher delivery efficiency and reduced off-target toxicity.
Using such protein-free RNA nanoparticles with RNA aptamers as anti-receptors will yield specificity as compared with protein anti-receptors and a lower antibody-inducing activity, thus providing an opportunity for repeated administration and treatment of chronic diseases.
The potential of the pRNA platform[3,103] for the construction of RNA nanoparticles to carry receptor-binding ligands for specific delivery of siRNA to target and silence particular genes have been explored for a variety of cancer and viral infected cells, including breast cancer, prostate cancer, cervical cancer, nasopharyngeal carcinoma, leukemia[53,54], and ovarian cancer, as well as coxsackievirus infected cells (Table 1). The data demonstrated that the pRNA nanoparticle is a nanodelivery platform that can be applied broadly to diverse medical applications.
Many factors affect the utility and effectiveness of a nanodelivery system. These include metabolic stability, induction of both innate and adaptive immunity, pharmacokinetic (PK) behavior and toxicological properties. It is generally believed that the optimal particle size for nanodelivery is 10 to 100 nm. This size range is large enough to avoid kidney filtration of particles less than 10 nm, but small enough to penetrate tissues and enter cells via receptor-mediated endocytosis, and facilitate intracellular trafficking, while also minimizing reticuloendothelial system (RES) mediated clearance. The commonly used lipid and polymer based nanoparticles with larger particle sizes and being hydrophobic cause accumulation in the liver kupffer cells and spleen macrophages, as well as lung macrophages . In addition, the induction of innate immunity and certain organ toxicity has been a major concern in siRNA therapeutics. Recently, it has been demonstrated that 2′-F-modified pRNA nanoparticles were chemically and metabolically stable in mice and demonstrated a favorable PK profile of plasma half-life (T1/2) of 5 to 10 hours, in contrast to T1/2 of 0.25 hour reported for siRNAs with similar chemical modifications (Fig. 7A), a clearance value (Cl) smaller than 0.13L/kg/hr, and a volume of distribution (Vd) of 1.2L/kg (Fig. 7B). With fluorescent and folate labeling, the pRNA nanoparticles were found to be specifically self-delivered to folate receptor positive xenograft tumor in mice upon systemic administration, with minimal accumulation in normal organs or tissues. These particles, composed of pure RNA, did not provoke interferon response, nor did they stimulate cytokine production in mice. Repeated intravenous administrations at doses up to 30 mg per kilogram did not cause toxicity in mice. The result of this and other pharmacological studies suggest that pRNA nanoparticles carry all the preferred pharmacological features to serve as safe drugs with broad clinical applications.
RNA can be manipulated with simplicity characteristic of DNA and bears versatile structure and catalytic function similar to proteins. It is an ideal building block in nanotechnology and nanomedicine. However, standing in awe of its sensitivity to RNase degradation has made many scientists hesitant to apply RNA nanotechnology. Recently, it has been reported that 2′-F modified pRNA retained its natural property for correct folding in dimer formation, appropriate structure in binding to the phi29 procapsid, as well as authentic function in driving the DNA packaging nanomotor, and producing infectious viral particles (Fig. 8). The data reveals that it is possible to manufacture RNase-resistant, biologically active and chemically stable RNA building blocks for application in nanotechnology.
pRNA is a 120-nucleotide molecule. Currently, chemical synthesis of RNA with 120 nucleotides in large quantities is very challenging. In addition, labeling of specific locations of pRNA requires the understanding of its modular organization. For in vivo trials or clinical applications, one technical hurdle is the lack of a scalable industry process to produce sufficient quantities of RNA. Recently, a two-piece approach has been reported for the construction of a functional 117-nucleotide pRNA using two synthetic RNA fragments with modifications at different locations. The resulting bipartite pRNA was fully competent in pRNA dimer formation, in the packaging of DNA via the nanomotoer and in the in vitro assembly of phi29 virions . The pRNA subunit assembled from two-piece fragments harboring siRNAs or receptor-binding ligands were also able to assemble into dimers. Dimers carrying different functionalities were able to bind cancer cells specifically, enter the cells and silence specific genes of interest. The pRNA nanoparticles were processed by Dicer to release the siRNA embedded in the nanoparticles. This two piece approach has also been demonstrated to be adapted for total chemical synthesis, enabling industrial scale manufacturing. The results pave a way toward the treatment of diseases using synthetic pRNA/siRNA chimeric nanoparticles.
The phi29 pRNA system is a unique delivery system, which takes advantage of the structural features of pRNA including the presence of two domains which fold independently and the facility of re-engineering to form different kinds of desired particles through interlocking loop-loop interactions or end palindrome sequences. The assembled nano-scale particles harboring functional moieties offer many advantages over the numerous other anti-cancer delivery platforms under development such as polyvalent delivery, controllable structure and precise stoichiometry, nanoscale size, targeted delivery, long haft life in vivo, no induction of interferon, and toll-like immunity, low or no toxicity, and non-induction of an antibody response to ensure repeated treatments. Consequently, pRNA nanoparticles delivery will potentially lead to an innovative therapeutic strategy for developing an effective and safe treatment for cancer and other diseases.
This work was supported by NIH grants EB003730, GM059944 and CA151648 to P.G.. We thank Bruce Shapiro, Qi-Xiang Li, Dong-ki Lee, Randall Reif, Daniel Binzel, and Wei Li for their helpful comments and discussion. P.G. is the co-founder of Kylin Therapeutics, Inc.
Publisher's Disclaimer: This is a PDF file of an unedited manuscript that has been accepted for publication. As a service to our customers we are providing this early version of the manuscript. The manuscript will undergo copyediting, typesetting, and review of the resulting proof before it is published in its final citable form. Please note that during the production process errors may be discovered which could affect the content, and all legal disclaimers that apply to the journal pertain.