Chitosan Hydrogel as siRNA vector for prolonged gene silencing
- Zhiwei Ma†1,
- Chuanxu Yang†2,
- Wen Song3,
- Qintao Wang1Email author,
- Jørgen Kjems2Email author and
- Shan Gao2Email author
© Ma et al.; licensee BioMed Central Ltd. 2014
Received: 18 January 2014
Accepted: 4 June 2014
Published: 19 June 2014
The periodontitis is one of the most prevalent diseases with alveolar resorption in adult people and is the main cause of the tooth loss. To investigate the possibility for protecting the loss of alveolar bone in periodontal diseases, a RNAi-based therapeutic strategy is applied for silencing RANK signaling using thermosensitive chitosan hydrogel as siRNA reservoir and vector.
The thermosensitive chitosan hydrogel was formed from solution (PH = 7.2, at 4°C) at 37°C within 8 minutes. The degradation rates of hydrogel were ~50% and 5% (W remaining/W beginning) in the presence and absence of lysozyme, respectively, over a period of 20 days. The concurrent cumulative in vitro release of Cy3-labeled siRNA from the hydrogel was 50% and 17% over 14 days, with or without lysozyme digestion, respectively. High cell viability (>88%) was maintained for cells treated with hydrogel loaded with RANK specific siRNA and RANK knockdown was prolonged for up to 9 days when cells were incubated with siRNA/hydrogel complex. In vivo release of siRNA was investigated in a subcutaneous delivery setup in mice. The fluorescent signal from siRNA within hydrogel was remained for up to 14 days compared to less than one day for siRNA alone.
Chitosan hydrogel can potentially serve as a suitable reservoir and vector for local sustained delivery of siRNA in potential therapy.
Most of periodontal diseases are highly destructive and characterized by loss of the periodontal ligament and alveolar bone, eventually causing tooth loss. It is possible to minimalize the disease progression to some extent via routine dental hygiene improvements but no traditional therapy can efficiently recover the reattachment of periodontal ligament tissues and induce the bone regeneration.
The alveolar bone damage is usually caused by abnormal activity of osteoclast. The receptor activator of NF-κB (RANK) and its ligand RANKL are key molecules for differentiation and activation of osteoclasts . When RANKL binds to RANK, it triggers downstream signaling that results in transformation of precursor cells to mature osteoclast. It would therefore be desirable to inhibit the pathway of osteoclast maturation via targeting RANK for prevention of alveolar bone loss.
RNA-interference (RNAi) is a post-transcriptional gene silencing process that is mediated either by synthetic small interfering RNAs (siRNAs) or endogenous microRNAs. RNAi has been established as an efficient tool for investigation of gene function due to its high specificity of gene silencing including genes associated with many diseases . Therapeutic RNAi applications have been well developed over the recent years and significant progress have been made in therapies for cancer , neurodegenerative diseases , infectious  and inflammatory lesions [6–8]. However, the main concern for siRNA therapeutics is the development of a safe delivery system for the siRNA that can protect siRNA from degradation and deliver it into specific cells without side effects. Among non-viral delivery systems, traditional lipid-based transfection system has been developed for decades and widely applied due to its well-controlled pharmacokinetic behavior and high transfection efficiency; however, the drawbacks are cytotoxicity and limited durability, which limit the application in vivo . Chitosan is a natural cationic polymer that can bind negative charged siRNAs via an electrostatic interaction to form complexes spontaneously in slightly acidic aqueous milieu. It has been comprehensively investigated for drug, plasmid  and siRNA delivery [11, 12], and considered a suitable transfection vehicle due to its low toxicity, low immunogenicity, low cost, and good biocompatibility . We have also successfully applied chitosan/siRNA derived therapies for arthritis and radiation-induced fibrosis in animal disease models [7, 8]. Hydrogel containing siRNA has also been demonstrated effective in cancer therapy  and chitosan-based hydrogel has been used as a reservoir for drug loading to enable sustained release of variously therapeutic agents at controlled positions [15, 16]. In particular, a chitosan-glycerol phosphate thermosensitive hydrogel, with improved biocompatibility [17, 18] and rapid solution-gel state shifting , has been employed to deliver ellagic acid , collagen composite  or ferulic acid  for the treatment of various diseases including cancer . In our study the chitosan hydrogel is loaded with RANK siRNA with aim to develop potential RNAi- based therapeutic strategy for periodontitis.
Three siRNAs, designed to target mouse RANK, were transfected in murine macrophage cell line, RAW264.7. Two of these siRNAs showed a strong knockdown of RANK mRNA expression (Additional file 1: Figure S1). siRNA2 was selected for further experiments and referred as siR-RANK.
Hydrogel mediated prolonged gene silencing
Cell viability assay
siRNA release test in vitro
To investigate whether siRNA is released as free siRNA or siRNA complexed with chitosan, a filter assay was performed. As expected, free siRNA, with a molecular weight of 13.3 kD, passes nearly completely through a membrane with MWCO of 100 kDa (Additional file 2: Figure S2). In contrast, less than 10% siRNA was recovered in the filter assay when formulated with chitosan indicating that the siRNA remains bound positively charged chitosan after release from the hydrogel.
Hydrogel degradation in vitro
siRNA release test in vivo
We have demonstrated that siRNA, loaded into chitosan hydrogel, is released in a sustained fashion both in vitro and in vivo. Using this system, RANK specific siRNA exhibited a prolonged specific silencing effect for up to 9 days in vitro without apparent cytotoxicity.
RNAi has recently proven a promising approach for the development of new treatment protocols for human diseases. However, the lack of suitably non-viral systemic delivery vehicles has limited its application in clinic where effective and prolonged silencing effects are needed. Compared to systemic delivery, local delivery systems can provide a relatively high drug concentration in the lesion areas and reduce side effects. For instance, local delivery of siRNA using biodegradable polymer enabled a scaffold to support and repair bone defects . However, the predetermined shape restricts the application for many kinds of lesions encountered in clinic. To address this, injectable hydrogel is widely applied for tissue engineering, also for drug delivery including siRNA delivery [25–27], due to its ability to undergo sol–gel phase transition.
We have successfully applied chitosan/siRNA therapies in several animal disease models with arthritis and radiation-induced fibrosis [7, 8]. Among chitosan-based hydrogels, the one cross-linked with β-glycerophosphate has been most extensively employed and already proven effective in several kinds of drug delivery [20–22, 25]. In addition, the chitosan-based gels have been used for tissue regeneration in periodontal disease . We have developed an injectable thermosensitive chitosan hydrogel system for siRNA delivery and observed prolonged knockdown efficacy for up to 9 days. The effect is more pronounced than in a previous collagen gel study where substantial knockdown of GFP was observed for only up to 6 days in GFP expressing HEK293 cells .
The in vitro siRNA release profile suggests that electrostatic interactions between the nucleotides and positively charged polymer slow down the release. In addition, diffusion through the biopolymer pores facilitated by biopolymer degradation may also control the release. This resembles the observation in a previous report for siRNA release from calcium cross-linked alginate with chitosan . In that study siRNA could only be released from the hydrogel when gradually degraded by an enzyme . In another study, gelatin hydrogel, incorporated with cationized gelatin (CG)-siRNA complexes, was enzymatically degraded by the treatment with collagenase to enable the release of siRNA . Similarly, we observed clear degradation in the presence of lysozyme, indicating that this enzyme is able to degrade the chitosan gel in vitro [29–31].
Compared to in vitro, siRNA was released more quickly in vivo, implying the existence of lysozyme or other degradation pathways in vivo . The chitosan hydrogel/siRNA system has previously been applied in tumor therapy in mice . They observed labelled siRNA uptake in tumour cells up to 270 μm away from the hydrogel edge 24 h post intra-tumoral injection, however, the half-life of siRNA in vivo was not addressed. The hydrogel was administrated twice weekly at a dose of 150 μg/kg body weight and resulted in significant antitumor effect . Similarly, the biodegradable hydrogel, poly-D, L-lactic acid-p-dioxanonepolyethylene glycol block co-polymer (PLA-DX-PEG) has been used as a carrier for Noggin specific siRNA in vivo, resulting in efficient silencing of the target mRNA expression and successfully induces the ectopic bone formation .
The RANK-RANKL system has been proven to play a vital role in the differentiation and activation of osteoclasts in periodontitis and silencing the RANK expression in osteoclast precursors may provide a new approach to prevent and convert the alveolar absorption in periodontitis. In this study, we demonstrate chitosan hydrogel could prolong gene silencing effect of siRNA up to 9 days in vitro. Theoretically, this extended release profile may be provide sufficient siRNA to prevent activation of osteoclasts and maintain the therapeutic effects on periodontitis for an extended period of time. In combination with the excellent biocompatibility we observed, our system may potentially serve as a suitable vector for continuous local delivery of RANK siRNA in periodontitis therapy.
In this study we have developed a chitosan-glycerol phosphate thermosensitive hydrogel enabling to functionally deliver RANK siRNA into cells. The hydrogel exhibited prolonged siRNA release profiles both in vitro and in vivo, accompanied with sustained gene silencing effect in cell. The next step will be to investigate its efficacy in animal periodontitis model and explore its potential to regenerate periodontal tissues.
siRNA target RANK screening
Sequence of siRNAs
Sense sequence (5′-3′)
Antisense sequence (5′-3′)
Mouse macrophage cell line, RAW264.7 (ATCC® TIB-71™), used as osteoclast precursor, was maintained in RPMI media (Gibco®) supplemented with 10% fetal bovine serum (Sigma), 1% penicillin-streptomycin (Gibco®) at 37°C in 5% CO2 and 100% humidity. Cells were seeded onto 24-well plate twenty-four hours before transfection. siRNA was transfected using the commercial reagent TransIT-TKO (Mirus Bio Corporation) at final siRNA concentration 50 nM. Cells were harvested at 48 hr post-transfection.
mRNA expression level was assessed by Quantitative Real-Time RT-PCR (qRT-PCR) following routine procedures of total RNA purification using TRIzol reagent (Invitrogen, Copenhagen) and reverse transcription using SuperScript® II Reverse Transcriptase (RT) kit (Invitrogen, Copenhagen). The comparative CT (threshold cycle) method described in the manufacturer’s protocol (Stratagene, Copenhagen) was used to quantitate the relative RANK mRNA expression level. The β-actin mRNA was amplified as an internal control to normalise the expression level. The primer sequences for RANK gene are, forward: 5’-TAGGACGTCAGGCCAAAGGACAAA -3’, reverse: 5’-AGGGCCTACTGCCTAAGTGTGTTT -3’, with a product size of 132 bp. Primer sequences for β-actin gene are, forward: 5’-ACACAGTGCTGTCTGGTGGT-3’, Reverse: 5’-CTGGAAGGTGGACAGTGAGG-3’ with a product size of 172 bp.
Formulation of chitosan hydrogel /siRNA complex
Chitosan (150 kDa, 95% deacetylation) was provided by HEPPE MEDICAL (Germany). Indicated chitosan was dissolved in 1% acetic acid (Sigma) at the concentration of 2% w/v. Sodium glycerophosphate (Sigma) were used as crosslink reagent and added dropwise into chitosan solution while stirring (pH 7.2, 4°C). Pre-calculated siRNA (5 μg) were added into the clear and homogeneous liquid solution (200 μl). The hydrogel spontaneously became solid during the incubation at 37°C for 8 minutes, which was ready for further experiments.
siRNA transfection mediated by hydrogel
Cytotoxicity of hydrogel/siRNA complex
The cell viability was determined by MTT assay at day 3 of hydrogel mediated transfection as described above (n = 3). MTT reagent (5 mg/ml, Sigma, Copenhagen) was then added to each well at 1:3 dilution, after removed transwells, rinsed with PBS and exchanged the medium. After incubation of 2 ~ 4 h at 37°C, the reaction was stopped by replacing of DMSO (Sigma, Copenhagen) while the color changes became visible. The relative absorbance (at 570 nm) was measured using a Victor X5 Multilabel Plate reader (PerkinElmer).
siRNA release test in vitro
To assess siRNA release profile, the Cy3-labled siRNA (5 μg) was formulated with chitosan hydrogel as described above. The hydrogel was immersed in 500 μl phosphate buffer (PBS, Gibco®) solution (pH 7.4) with or without lysozyme (0.5 mg/ml, Sigma). At pre-determined intervals, all of the supernatant was drawn and replaced by the fresh buffer accordingly. The fluorescence intensity from the supernatant was measured by fluorescence plate reader (FLUOstar OPTIMA) and PBS solution was used as blank control.
To investigate whether siRNA in release solution as free or chitosan complexed siRNA, Cy3-labled siRNA was encapsulated in chitosan hydrogel (n = 3). After gelation, 500 μl of PBS was added and incubated 2 h at 37°C. The PBS solution was collected and 250 μl the solution was loaded on to a centrifugal device with molecular weight cut off (MWCO) of 100 kDa (Pall Corporation) and centrifuged at 3000 g for 5 min. The Cy3 fluorescent intensity of filtered solution was measured by FLUOstar OPTIMA (BMG Labtechnologies) and normalized to input solution. As a non-particulate control, free Cy3-siRNA was also loaded on a centrifuge device treated similarly.
Hydrogel degradation in vitro
To further understand the mechanism of siRNA release from the hydrogel, the hydrogel degradation was assessed. Briefly, 1ml chitosan hydrogel solution was placed into 37°C incubator to form the hydrogel. The hydrogel, treated using three concentration of lysozyme (0, 0.1, 0.5 g/L), was quickly frozen with liquid nitrogen for 5min and totally freeze-dried before precisely weighed by electronic balance. The percentage of mass loss was determined by measuring hydrogel weight at initial time point (Wi) and weight at different time points pre-designed (Wd), and calculated by ((Wi-Wd)/Wi). After gold coating, the freeze-dried sample was also observed with Field Emission Scanning Electron Microscope (FE-SEM).
siRNA release test in vivo
To evaluate siRNA release within hydrogel in vivo, BALB/c female mice (Taconic Europe, Ll. Skensved, Denmark) were chosen. All procedures of animal work were approved by “The Experimental Animal Inspectorate in Denmark” under The Danish Veterinary and Food Administration, Ministry of Food, Agriculture and Fisheries.
Hair from the back and the abdomen was shaved to avoid autofluorescence during scanning. Cy5-labelled siRNA/chitosan hydrogel formulation in 50 microliter sodium acetate buffer (containing 5 μg siRNA duplex) was subcutaneously injected into the left flank region of mice. The unformulated Cy5-labelled siRNA in PBS with the same volume was administrated as control. The mice were scanned using an IVIS® 200 imaging system (Xenogen, Caliper Life Sciences) before and right after injection followed by 1 hr, 2 hrs, 1 day, 2, 3, 7 and 14 days post injection. The scanning was performed under anesthesia with 2.5% isoflurane. Cy5 excitation (λex = 640 nm) and emission (λem = 700 nm) filters were used. Total emission from inflicted areas (Region of Interest, ROI) of each mouse was quantified using Living Image 4.0 software package. According to the user instruction, the radiant efficiency (RE) of injection sites was measured (photons/sec/cm2/sr)/ (μW/cm2), which is presented radiance/illumination power density [33, 34].
This work was supported by grants from the Nature Science Foundation of China (NSFC 81271137) and the Lundbeck Foundation - Lundbeck Foundation Nanomedicine Center for Individualized Management of Tissue Damage and Regeneration. We thank San Hein for his supervision of chitosan preparation and Menglin Chen for her kindly help in hydrogel release test in vitro. We thank Rita Rosendahl and Claus Bus for their excellent technical assistance, as well as Frederik Dagnæs-Hansen for his arrangement of animal works.
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