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Spinal cord injury (SCI) commonly leads to lifelong disability due to the limited regenerative capacity of the adult central nervous system. Nanomicelles can be used as therapeutic systems to provide effective treatments for SCI. In this study, a novel triblock monomethyl poly(ethylene glycol)-poly(l-lactide)-poly(trimethylene carbonate) copolymer was successfully synthesized. Next, polymeric nanomicelles loaded with zonisamide (ZNS), a Food and Drug Administration-approved antiepileptic drug, were prepared and characterized. The ZNS-loaded micelles (ZNS-M) were further utilized for the treatment of SCI in vitro and in vivo. The obtained ZNS-M were ~50 nm in diameter with good solubility and dispersibility. Additionally, these controlled-release micelles showed significant antioxidative and neuron-protective effects in vitro. Finally, our results indicated that ZNS-M treatment could promote motor function recovery and could increase neuron and axon density in a hemisection SCI model. In summary, these results may provide an experimental basis for the use of ZNS-M as a clinically applicable therapeutic drug for the treatment of SCI in the future.
Spinal cord injury (SCI) can result in devastating lifelong disability for patients and their families. In developing countries, the incidence rates of SCI have ranged from 12.7 to 29.7 cases per million people in the past few decades.1 According to a large-scale epidemiological study of spinal injuries in mainland China, SCI accounted for 0.74% of all traumas from 2001 to 2007.2 Currently, medical treatment options after a spinal cord trauma are limited. The drug used clinically to treat acute SCI is an extremely large dose of methylprednisolone (MP) administered within the first 8 h post-injury.3 However, the efficacy of MP treatment is highly controversial due to the serious side effects associated with this glucocorticoid, including myopathy, infections and gastric bleeding.4,5 Moreover, there is no successful treatment for any of the main types of dysfunction that occur after SCI, including chronic severe pain, autonomic dysreflexia and bladder, bowel and sexual dysfunction.3 Therefore, the development of novel therapeutic strategies that target this condition is imperative.
The pathophysiology of SCI consists of a primary injury along with sequential secondary damages emanating from a multicascade of pathological mechanisms, which often leads to permanent motor and sensory deficits due to the limited regenerative capacity of the adult central nervous system (CNS).6 Oxidative stress and reactive oxygen species (ROS) production play a predominant role in the secondary injury mechanisms of SCI.7 Oxidative damage most likely contributes to calpain activation by the disruption of Ca2+ homeostasis. It is also known to exacerbate excitotoxic glutamate and to compromise the neuronal homeostatic mechanisms that either directly or indirectly regulate intracellular Ca2+, including Ca2+ ATPase, Na+–K+ ATPase, Na+–Ca2+ exchanger and mitochondrial Ca2+ sequestration.8,9 Therefore, therapeutically targeting oxidative enzymes will prevent axonal demyelination, preserve oligodendrocyte integrity and spare neuronal loss.10
Zonisamide (1,2-benzisoxazole-3-methanesulfonamide; ZNS) is an antiepileptic drug that has already been approved for clinical use. Several clinical studies have reported the wide clinical spectrum of ZNS against both psychiatric and neurological disorders. The major antiepileptic action mechanisms of ZNS include inhibition of the voltage-gated Na+ channel, the T-type voltage-sensitive Ca2+ channel, the Ca2+-releasing system and neuronal depolarization-induced glutamate release.11 Another previous study has shown that ZNS is an effective inhibitor of monoamine oxidase B (MAO-B) in vitro and in vivo.12 There is also information available showing that ZNS can induce protective effects against oxidative stress and the antioxidant redox system through modulation of cytosolic Ca2+ concentrations in neuronal cell lines.13 In addition, it has been proven that ZNS improves clinical outcome when used as an adjuvant in the treatment of Parkinson’s disease (PD), possibly due to its ability to promote the recovery of degenerating dopaminergic neurons.11
Micelles are formed by the self-assembly of amphiphilic block copolymers in aqueous environment, and they can function as solubilizing agents for hydrophobic drugs.14,15 The hydrophobic segments of micelles become packed together in aggregates (core), which serve as a storage site for poorly water-soluble drugs and can act as a nanodepot for these agents.16,17 The common advantage of these drug delivery systems is that micelles are resistant to glomerular filtration, which could extend their retention time in the blood.18 Furthermore, micelles can facilitate the passage of drugs through the blood–brain barrier and blood–spinal cord barrier (BSCB), increasing therapeutic efficacy and safety compared to conventional pharmaceutical dosage forms.19 There have been several reports of biodegradable polymeric micelles for SCI treatment.20 Chen et al21 improved the bioavailability of MP in the spinal cord using poly(ethylene oxide)-poly(propylene oxide)-poly(ethylene oxide) (PEO-PPO-PEO) polymeric micelles as a delivery vehicle. In addition, self-assembled monomethoxy poly(ethylene glycol)-poly(d,l-lactic acid) di-block copolymer micelles (MPEG-PDLLA) have been demonstrated to be effective in restoring compound action potentials (CAPs) of the injured spinal cord, decreasing calcium influx into axons and promoting the recovery of locomotion function in an SCI rat model.22
Polyethylene glycol (PEG) is a fusogen that can restore the integrity of severed cell membranes.22,23 This water-soluble polymer is an ideal candidate for neural restoration in the clinic. PEG-based nanoparticles, including PEG-polyester, monomethoxy PEG-poly(d,l-lactic acid), PEG-silica and poly(lactic-co-glycolic acid), were demonstrated to act in CNS neuroprotection by repairing damaged axonal membranes through an intrinsic antioxidant mechanism.22,24–27 Poly(trimethylene carbonate) (PTMC) is a highly elastic polymer that was investigated for potential biomedical applications in soft tissue engineering and drug delivery systems.28 Block copolymers and terpolymers with polycarbonate segments have become promising bioresorbable materials. By changing the ratio and the total number of segments of the copolymers, the structure of micelles and their composition can be controlled.29,30 In addition, the mechanical properties, the hydrophilic–hydrophobic balance and the biodegradation rate of the materials can be easily modified by changing the block lengths and the composition of the polymers.31
In this study, we first synthesized a monomethyl poly(ethylene glycol)-poly(l-lactide)-poly(trimethylene carbonate) (MPEG-PLLA-PTMC) triblock copolymer. Furthermore, ZNS-loaded MPEG-PLLA-PTMC nanomicelles (ZNS-M) were successfully prepared. Finally, the monodisperse polymeric micelles were characterized by particle size distribution, transmission electron microscope (TEM), X-ray diffraction (XRD) and Fourier transform infrared (FTIR) spectroscopy, among others, and its neuroprotective effect was investigated in vitro and in vivo.
ZNS was purchased from Aike Chemicals (Ningbo, China). Monomethyl poly(ethylene glycol) (MPEG; Mn =1.98×103; Fluka, Sigma-Aldrich Co., St Louis, MO, USA), l-lactic acid (l-LA; Sigma-Aldrich, USA), 1,3-trimethylene carbonate (TMC; Huizhou Foryou Medical Devices, China) and stannous octoate (Sn(Oct)2; Sigma-Aldrich Co., St Louis, MO, USA) were used without purification. Methanol (high-performance liquid chromatography [HPLC] grade; Thermo Fisher Scientific, Waltham, MA, USA), thiazolyl blue tetrazolium bromide (MTT; Sigma), Cy3 Goat anti-Rabbit kit (Boster, Wuhan, Hubei, China) and FITC Goat anti-Mouse kit (Boster) were used as received. All the organic solvents used in this study were of analytical reagent (AR) grade and were used as received.
The astrocyte rat CTX TNA2 (ATCC® CRL-2006™) cell lines were cultured in Dulbecco’s Modified Eagle’s Medium (DMEM; HyClone, Logan, UT, USA) with 10% fetal bovine serum (FBS; Gibco, Mulgrave Victoria, Australia) and 1% penicillin/streptomycin (Gibco). The cells were incubated at 37°C with a humidified 5% CO2 atmosphere.
Female Sprague-Dawley rats (HFK Bioscience Co., LED, Beijing, China) weighing 250±20 g were used as spinal cord hemisection models to evaluate neuroprotective effects and functional recovery in vivo. All mice were quarantined for a week before treatment and provided with standard laboratory animal living conditions. All animal procedures in this study were performed following protocols approved by the Institutional Animal Care and Treatment Committee of Sichuan University (Chengdu, People’s Republic of China).
The copolymer with an MPEG-PLLA-PTMC ratio of 2000–1000–1000 was synthesized by ring-opening polymerization of l-lactide and TMC initiated by MPEG. Briefly, MPEG (10 g), l-lactide (5 g) and TMC (5 g) were introduced into the reaction vessel under a dry nitrogen atmosphere. The reaction was catalyzed by Sn(Oct)2 and kept at 130°C for 24 h. The purified MPEG-PLLA-PTMC copolymer was kept in a desiccator and characterized by 1H-NMR (Varian 400 spectrometer; Varian Medical Systems, Palo Alto, CA, USA). In addition, the MPEG-PLLA-PTMC copolymer samples were dissolved in tetrahydrofuran (THF) to determine the molecular weights and distribution by GPC (1100 series; Agilent, Santa Clara, CA, USA).
ZNS-M were obtained through a single-step solid dispersion method. Briefly, ZNS and MPEG-PLLA-PTMC copolymer were dissolved in 25 mL acetone under mild stirring at room temperature. Then, the mixed solution was evaporated using a rotary evaporator at 37°C under gradually increasing vacuum. The resulting residue was dissolved in 4 mL normal saline (NS) at 37°C to form ZNS-loaded micelles. The obtained ZNS-M were filtered through a 0.22 mm syringe filter (Millex-LG; EMD Millipore, Billerica, MA, USA) and frozen by liquid nitrogen to avoid collisions before lyophilizing. The lyophilized powder was kept at 4°C before further use.
The stability of ZNS-M in aqueous solution was evaluated qualitatively at room temperature over 48 h. Precipitation implied the instability of ZNS-M. In addition, the particle size distribution of ZNS-M was determined within 30 min by dynamic light scattering (DLS) using a Malvern Nano-ZS 90 laser particle size analyzer at 25°C. All reported experimental results were performed in triplicate as mean ± standard deviation (SD).
The morphological characteristics of ZNS-M were investigated by TEM (Tecnai G2 F20 S-TWIN electron microscope, FEI Co.) as previously described.23
Drug loading (DL) and encapsulation efficiency (EE) of ZNS-M were estimated by HPLC (Waters Alliance 2695). Briefly, 10 mg of lyophilized ZNS-M powder was dissolved in 0.1 mL of methanol. The samples were analyzed in the mobile phase, containing 65% (v/v) methanol and 35% (v/v) ultrapure water, at a flow rate of 1 mL/min. Detection was performed on a Waters 2996 detector. Chromatographic separations were performed on a reversed-phase C18 column (4.6×250 mm – 5 μm, Grace Analysis column) at 28°C. The detection wavelength for ZNS was set at 240 nm, and the elution time of ZNS was 2.218 min under the chromatographic conditions described earlier. The concentration of ZNS in the solution was determined by HPLC and calculated using the following equations:
XRD (X Per Pro MPD DY 1291; PHILIPS, Amsterdam, the Netherlands) measurements were performed to study the phase and crystallinity of the ZNS-M powder at a scanning rate of and a step size of 0.03° in the 2θ range from 5° to 50°.
The chemical structure of the ZNS-M powder was determined by FTIR spectroscopy (NICOLET 200SXV; Nicolet, New York, NY, USA). Infrared spectra were recorded in a wavenumber range of 400–4,000 cm−1.
The release kinetics of ZNS from ZNS-M were determined by a dialysis method. A solution of ZNS-M and free ZNS in dimethyl sulfoxide (DMSO) (0.5 mL, 0.5 mg/mL) were placed into dialysis bags (molecular weight cutoff, 3.5 kDa). The dialysis bags were incubated in 30 mL of phosphate buffer solution (PBS, pH 7.4) containing Tween-80 (0.5 wt%) at 37°C with gentle shaking (100 rpm). At predetermined time points, 1 mL of the medium was collected and stored at −20°C for further analysis. The remaining medium was removed and replaced by prewarmed fresh PBS. The collected samples were quantified using HPLC. All results are presented as the mean of five sample runs, expressed as the mean ± SD.
The CTX TNA2 cells were seeded at 1×103 cells per well into a 96-well plate and incubated for 12 h at 37°C in a humidified atmosphere containing 5% CO2. After replacing with fresh medium, the cells were exposed to 500 μM H2O2 solution and were treated with free ZNS (dissolved in DMSO), ZNS-M and blank micelles (M) at different concentrations (0–50 μM). For the cytotoxicity test, H2O2-untreated cells were incubated with free ZNS, ZNS-M and blank M at different concentrations (0–50 μM). After the treatment, the cell viability was estimated with the MTT assay at particular time intervals according to previously published protocol.23
The cortical neuron cells were separated from embryonic SD mice. Briefly, after anesthesia, the cerebral cortexes of the embryonic mice were carefully dissected and washed with PBS (pH 7.4) on ice. The specimens were dissociated by 1 mL pipette and digested with 1 mg/mL collagenase II (Sigma-Aldrich) for 15 min at 37°C in an incubator. The collagenase was inactivated by adding DMEM with 10% FBS. After centrifugation, the supernatant was discarded and the pellet was resuspended in Neurobasal®-A Medium with 2% B-27® Serum-Free Supplement (Thermo Fisher Scientific, Waltham, MA, USA). The resulting solution was incubated in a 75 cm2 culture dish at 37°C with 5% carbon dioxide. The culture medium was changed every 3 days. Free ZNS, ZNS-M and blank M were added into the culture medium at a final concentration of 20 μM within 24 h.
After 2 weeks, the neuronal cells were fixed with prewarmed 4% paraformaldehyde solution (Boster) and blocked in 5% goat serum with 0.1% Triton-X (Sigma). After 30 min, the cells were immunostained by the anti-MAP2 (1:1,000 dilution; Abcam, Cambridge, UK) and the anti-neurofilament-H (1:200 dilution; CST, Boston, USA) antibodies. The neuron cells and neurite lengths were observed under microscope. Quantification of the axon length and the average branch points was performed by counting the numbers randomly under high-power visual fields.
Surgeries were performed after anesthetizing the SD rats with chloral hydrate solution (10 wt%, 0.3 mL/100 g; Kelong, Chengdu, China). A 2 cm longitudinal skin incision was centered over the T9–T10 spinous process along the midline. Without disrupting the dura mater, the T10 spinal segment was exposed by removing the dorsal part of the vertebra. Next, the exposed cord was hemi-cut on the right side by a sharp blade. Finally, the muscle and skin layers were sutured.
After 24 h, ~96% of the injured rats had survived. The animals were randomly divided into four main experimental groups (seven rats per group) receiving different treatments. The SCI rats were treated intravenously with ZNS-M (10 mg/kg ZNS), free ZNS (10 mg/kg ZNS), equivalent blank M and NS both 6 h and 4 days after surgery. Before the injection, the lyophilized powder was redissolved in NS with 1 mg/mL ZNS at 37.5°C.
After anesthesia, each rat was placed on the fixation system in prone position. The experiments were performed on a 3.0 T clinical MR scanner (Siemens Trio Tim), using a rat phased array RF coil (CG-MUC18-H300-AS; Chengguang Medical Technologies Co., Ltd, Shanghai, China). The spine MRIs were scheduled at 4 weeks post-SCI. Images of the injured regions were acquired in the sagittal planes. The sequence protocol included T1-weighted, 256×256 matrix, field of view (FOV) 80, slice thickness 1 mm, echo time (TE) 13/92 ms and repetition time (TR) 505/3,000 ms, respectively.
Functional recovery of the hind limbs was evaluated using the Basso-Beattie-Bresnahan locomotor rating scale (BBB score)32 at 1 week after treatment and subsequently every 2 weeks. The evaluations were performed using a double-blind method, and the average scores in each group were calculated.
Specific proteins were identified using immunohistochemical staining as described in our previous study. Briefly, the samples of SCI were dissected and post-fixed in 4% paraformaldehyde over 24 h. After being blocked by 5% goat serum, the coronal sections (4 μm) were stained with the anti-glial fibrillary acidic protein (GFAP) antibody (1:5,000 dilution; Abcam) and the anti-neurofilament-H antibody (1:200 dilution; CST). After incubation with the primary antibody at 4°C for 12 h, the sections were incubated with the fluorescent secondary antibody kits (Cy3 Goat anti-Rabbit and FITC Goat anti-Mouse) according to the manufacturer’s instructions. Nuclei were counterstained for 3 min using DAPI. All samples were examined with a fluorescence microscope (Leica DM IRE2; Leica Microsystems, Wetzlar, Germany). The heart, liver, spleen, lung and kidneys were also excised and stained with hematoxylin–eosin (H&E). Quantification of neurofilament and GFAP was performed by counting the number of positive cells in 15 high-power visual fields randomly. More than five sections of each sample were considered.
Statistical analysis was carried out using SPSS 15.0 software (Chicago, IL, USA). Comparisons of experimental data in different groups were performed using one-way analysis of variance (ANOVA). Results with P<0.05 were considered statistically significant.
The biodegradable MPEG-PLLA-PTMC copolymer was successfully synthesized by the ring-opening polymerization of l-LA and TMC initiated by MPEG (Figure 1). The number-average molecular weights (Mn) of the MPEG-PLLA-PTMC copolymers were calculated by 1H-NMR (Figure 2A). GPC results (Figure 2B) show that only one single peak was present. The Mn and Mw of MPEG-PLLA-PTMC were 4.40×103 and 5.97×103, respectively. The polydispersity index (PDI) of the copolymer was 1.5.
The ZNS-loaded MPEG-PLLA-PTMC nanomicelles were prepared by a one-step solid dispersion method and were characterized in detail. As illustrated in Figure 3, blank M (10 mg/mL) and ZNS-M (10 mg/mL) were stable in NS with good solubility at room temperature. However, the solubility of free ZNS (10 mg/mL) in water was poor (Figure 3C). The particle size of ZNS-M was 42.7±3.2 nm (Figure 3B) with a PDI of 0.167±0.026. Furthermore, the properties of different mass ratios of ZNS-M (3 wt%, 5 wt%, 8 wt%, 10 wt% and 13 wt%) were evaluated. The results showed a reasonable increase in DL with a decrease in EE and stability time (Table 1). According to the TEM results, ZNS-M (5 wt%) were well-dispersed spheres with a mean diameter of ~50 nm.
FTIR spectroscopy shows the main characteristic bands of ZNS and the MPEG-PLLA-PTMC copolymer. In the spectrum of ZNS-M, the peaks at 1,605 cm−1 and 749.2 cm−1, which were not detected in the blank MPEG-PLLA-PTMC micelles, were shifted lower in comparison to free ZNS (Figure 4A). Moreover, the XRD spectra of free ZNS, blank M and the ZNS-M crystals are shown in Figure 4B. The specific diffraction peaks of ZNS disappeared in the XRD spectrum of ZNS-M, indicating that ZNS was incorporated in the MPEG-PLLA-PTMC micelles.
The in vitro drug release behavior of ZNS-M was determined by HPLC. As shown in Figure 5, ZNS was sustainably released from ZNS-M over a 10-day extended period. On the other hand, free ZNS in DMSO showed faster release behavior than ZNS-M. In the first 8 h, ~30.32%±4.57% of ZNS was released from ZNS-M, which was lower than the amount released in the free ZNS group (80.08%±3.29%, P<0.05). The cumulative release of ZNS-M was ~75.167%±3.27% over the period of 11 days, which was much lower than the cumulative release of the free ZNS group (95.997±2.31, P<0.05). Thus, the MPEG-PLLA-PTMC copolymer micelles could facilitate the sustained release of ZNS as a drug delivery system.
To investigate the antioxidant activity of ZNS-M in vitro, the number of viable H2O2-treated CTX TNA2 cells was quantified by MTT assay. After drug treatment for 24 h and 48 h, the absorbance of the cells in the ZNS-M group was significantly increased compared to the DMSO and the control group (P<0.05) (Figure 6A and B). The free ZNS group also showed a higher viable cell number than the DMSO and the control group at 24 h and 48 h, respectively (Figure 6A and B). Thus, ZNS may provide a neuroprotective effect against oxidative stress in nervous tissue. For H2O2-untreated cells, no significant differences were observed in all groups within 24 h (Figure 6C). However, it was notable that the absorbance of the ZNS-M group was lower than that of the other four groups (Figure 6D) at 48 h. These results indicated that ZNS-M can inhibit the growth of neuroglia cells in vitro.
The axon lengths of primary neuron cells were measured under high-power visual fields after treatment with the drugs. In the ZNS and ZNS-M groups, the axon lengths of neurons were obviously elongated (Figure 7A and B) compared to those in the control group after 2 weeks. In addition, the number of branch points was also increased in the ZNS and ZNS-M groups (Figure 7A and C). However, there was no significant difference in either the axon lengths or the branch points between the ZNS group and the ZNS-M group (Figure 7B and C). These results indicated the abilities of ZNS-M to enhance neurite elongation in primary neurons.
After 1 month, the pathological change of SCI was examined by a 3.0 T MRI unit. The different degrees of scarring tissue adhesion were observed in each group (Figure 8Aa–d). However, in the ZNS-M group (Figure 8Ac), the atrophied area of the spinal cord was obviously smaller than that in other SCI groups.
To further evaluate motor function in the SCI models, the locomotor rating scale was performed every 2 weeks. As shown in Figure 8B, the hind limbs of all experimental animals (except the sham group) were paralyzed after the injury. The BBB scores of the sham group were always at the highest level because the nerve function was not damaged. The mean BBB scores of the control group were lower than those of the ZNS and ZNS-M groups at each time point. During the first 14 days, the average BBB scores of the ZNS group were slightly higher than the scores of the ZNS-M group. From the 14th day, the scores of the ZNS-M group continuously increased from 5.5 to 12 (21 days after injury), exceeding the scores of the free ZNS group. Notably, significant differences gradually emerged between each groups after 4 weeks post-SCI (P<0.05). These results suggested that ZNS-M plays a role in the improvement of neurological function.
The histopathological manifestations in injured spinal tissues at 4 weeks post-operation were analyzed. Immunofluorescence staining showed that NF-positive nerve fibers were distributed in the middle areas of the spinal cord in the sham group (Figure 9A). The number of NF-positive nerve fibers in the ZNS-M group was significantly higher than in the free ZNS and control groups (Figure 9A). Additionally, in the area of the spinal injury, nerve fibers extended over a long distance (Figure 9A), indicating that ZNS-M treatment is conducive for nerve fiber repair in vivo. GFAP is an important marker located in glial cells. Immunofluorescence staining showed intense GFAP distribution at the injured site of the spinal cord in the ZNS-M; however, ZNS-M treatment did not result in the same significant reduction in the number of GFAP-positive neurons that it did in vitro (Figure 9B). In addition, the safety evaluation indicated that the injected ZNS-M, free ZNS and blank M at 10 mg/kg displayed no acute toxicity in vivo (Figure 10).
Strategies for treating SCI can be broadly divided into two main types: neuroprotection and regeneration. The detrimental effects of oxidative stress commence immediately after the primary impact of SCI, causing membrane and cellular damage.33,34 Thus, antioxidative therapy is a reasonable approach to arrest and reverse inflammatory response in SCI. ZNS is a Food and Drug Administration-approved antiepileptic drug in clinical practice. It has been reported that ZNS is a MAO-B inhibitor that is effective in lessening neuron-specific oxidative stress.12 It has been proposed that the mechanisms of its neuroprotective effects include free radical scavenging and reducing oxidative stress. The predominant feature of SCI is damage to axon tracts, resulting in loss of communication between the CNS and the body.35,36 Thus, the challenge for spinal cord regeneration is not simply to fill in a lesion with a new cellular matrix but rather to recapitulate the highly organized axon pathways that were lost.37 In addition to reforming neural circuits, axon growth is an important component of regeneration. A recent study suggested that ZNS is able to enhance neurite elongation and neurite regeneration of primary motor neurons.38 Thus, we expect that the drug function mechanism of ZNS will play a role in the treatment of SCI.
Nanotechnology-based drug delivery has become an emerging strategy that provides particular advantages for neuroprotection.33 Micelles have been used as drug carriers for many years. Hydrophobic drugs can be encapsulated in the core to improve their water solubility, stability and circulation half-life. In previous studies, PEG has been commonly used as the hydrophilic moiety of micelles due to its solubility.23,39 The amphiphilic polymeric components (eg, MPEG-PDLLA micelles) are able to seal the damaged cell membranes and play a neuroprotective role.22 In this study, a novel MPEG-PLLA-PTMC triblock copolymer was successfully synthesized by ring-opening polymerization. In subsequent studies, the ZNS-loaded MPEG-PLLA-PTMC micelles (ZNS-M) were successfully prepared by a one-step solid dispersion method without the use of any surfactants or toxic organic solvents. Detailed characterization of ZNS-M showed their favorable stability, along with their small particle sizes and high EE and DL (Table 1; Figure 3). The results of TEM further affirmed that ZNS-M were stable and monodisperse in aqueous solution (Figure 3D), which suggests that they could be used for intravenous applications. The main characteristic bands in the FTIR and XRD spectra indicated that ZNS was completely and amorphously encapsulated in the core–shell structure of the MPEG-PLLA-PTMC micelles (Figure 4). The lasting release behavior of ZNS-M was observed in vitro (Figure 5). However, complete release was not seen in this drug release studies, which may be due to the drug aggregating over time in the release medium or during the freezing of the release samples before measurement.16,40,41
Inflammation plays a role in the progression of secondary SCI. The activated microglial cells can induce oxidative stress when cultured with neuronal cells.42,43 Although the response is natural, oxidative stress can be detrimental to cells that are already undergoing stress. Herein, we identified that ZNS-M effectively inhibited H2O2-induced cell death in rat astrocyte cells. The results indicated that ZNS-M and free ZNS were protective against oxidative stress (Figure 6A and B). The viable cell number in the ZNS-M group was significantly higher than other groups. This result may partially stem from the PEG segment, which has the ability to recover axonal integrity.19 In addition, ZNS-M exhibited an inhibitory effect on neuroglia cell growth, which may help inhibit glial scar formation.44 In addition to the antioxidant effects, it was also shown that ZNS has the ability to promote neurite elongation in mouse primary motor neurons in a dose-dependent manner.38 In this study, we found that the axon lengths of neurons were obviously elongated in the ZNS and ZNS-M groups (Figure 7). Enhanced neurite elongation in primary motor neurons and axonal regeneration may partially account for the enhancements of BDNF and Ntrk2 by ZNS,38 although the underlying mechanisms remain unknown.
An ideal treatment for inducing axon regeneration in an injured spine should reduce growth-inhibitory factors at the lesion site and be administrable as a medication after the injury.45,46 Many antioxidants show promising results in vitro, but their translation in vivo is limited by a short half-life, limited efficiency and metabolism. In this study, the stable ZNS-loaded micelles and free ZNS were administered by injection of the caudal vein. To determine whether ZNS-M could improve the functional outcomes in SCI in animal models, we performed a behavioral study to evaluate the hind-limb functional recovery using the BBB locomotor rating scale. Three days after surgery, the BBB scores began to show differences among the treatment groups, indicating that the function of the hind limbs was gradually recovering. Importantly, the recovered function in the ZNS-M treatment group was better than that of the free ZNS group and the control group 21 days after SCI (Figure 8B). In addition, the results shown by MRI revealed that the atrophied area of the spinal cord in the ZNS-M group (Figure 8Ac) was obviously smaller than the area in the other SCI groups (Figure 8Ab and d). These results signified that ZNS-M treatment could promote motor function recovery after SCI. We believe that ZNS loaded in nanoscale micelles could prevent glomerular filtration, thus extending the retention time of the drug in the blood. Compared to free ZNS, this prolonged effective drug duration of released ZNS may provide better neuroprotective effects in vivo.25,47,48
Neuron and axon density are critical indicators of anatomical recovery from SCI.43,49 In histopathologic examination, a statistically significant increase of NF was observed in the ZNS-M group (Figure 9). Injury to neurons stimulates a rapid production of superoxide, resulting in cell death.3 Thus, inhibition of the oxidase enzyme could result in improvements in functional recovery. However, ZNS-M treatment in vivo did not result in a reduction in the number of GFAP that was as significant as the reduction observed in vitro. The reason for this result is unclear, and whether astrocyte scar formation benefits axon regeneration remains controversial.49 In addition, the toxicity evaluation demonstrated that the ZNS-M is a safe treatment for injection in vivo (Figure 10).
In this work, a novel triblock MPEG-PLLA-PTMC copolymer was successfully synthesized. Polymeric micelles loaded with ZNS were prepared and evaluated for the treatment of SCI in vitro and in vivo. The controlled-release ZNS-M were 42.7±3.2 nm with good solubility and stability at room temperature. ZNS-M plays a neuron-protective role by antioxidative effect in vivo. In addition, ZNS-M treatment could promote motor function recovery in a hemisection SCI model. Therefore, ZNS-M may be a clinically applicable therapeutic drug for SCI in the future.
This work was financially supported by the National Natural Sciences Foundation of China (81571259) and the National S&T Major Project (2011ZX09102-001-10).
The authors report no conflicts of interest in this work.