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Molecules 2018, 23(8), 2061; doi:10.3390/molecules23082061

Article
Aromatic Thioacetal-Bridged ROS-Responsive Nanoparticles as Novel Gene Delivery Vehicles
College of Chemistry and Environmental Protection Engineering, Southwest Minzu University, Chengdu 610041, China
*
Authors to whom correspondence should be addressed.
Received: 16 July 2018 / Accepted: 11 August 2018 / Published: 17 August 2018

Abstract

:
In this report, a series of polycations are designed and synthesized by conjugating reactive oxygen species (ROS)-responsive thioacetal-linkers to low molecular weight (LMW) polyethylenimine (PEI) via ring-opening polymerization. Their structure–activity relationships (SARs) as gene delivery vectors are systematically studied. Although the MWs of the target polymers are only ~9 KDa, they show good DNA binding ability. The formed polyplexes, which are stable toward serum but decomposed under ROS-conditions, have appropriate sizes (180~300 nm) and positive zeta-potentials (+35~50 mV). In vitro experiments reveal that these materials have low cytotoxicity, and higher transfection efficiency (TE) than controls. Furthermore, the title polymers exhibit excellent serum tolerance. With the present of 10% serum, the TE of the polymers even increases up to 10 times higher than 25 KDa PEI and 9 times higher than Lipofectamine 2000. The SAR studies also reveal that electron-withdrawing groups on the aromatic ring in 4a may benefit to balance between the DNA condensation and release for efficient gene transfection.
Keywords:
reactive oxygen species (ROS); stimuli responsive; gene delivery; cationic polymer; non-viral vectors

1. Introduction

Gene therapy is considered to be one of the most promising approaches to treating various human genetic and acquired diseases, such as cancers, aging, diabetes, and cardiovascular diseases [1]. Safe and effective gene delivery vectors are a prerequisite for successful gene therapy [2,3]. Due to the high transfection efficiency (TE), viral carriers are a commonly used method of gene delivery. However, their immunogenicity, toxicity, limited DNA packaging capacity, and difficulty in large-scale production have impeded their development and clinic applications [4,5]. In attempt to overcome these barriers, a broad range of versatile and efficient non-viral gene vectors have been developed. Cationic polymers, as one class of non-viral gene vectors, have acquired increasing attention due to their easy preparation and modification in recent years [6,7,8].
Gene transfection with cationic polymers needs to overcome multiple delivery barriers, including the formation of polymers/DNA complexes (polyplexes) and their initial binding to the cell surface, endocytosis, endosomal escape, nuclear entry, and final expression [9,10,11]. “Golden standard” 25 KDa PEI is the most widely studied polymeric carrier, both in vitro and in vivo [12]. Unfortunately, high molecular weight (HMW) PEI remains cationic under physiological conditions and is not biodegradable, resulting in its well-known cytotoxicity, the difficult release of genes and low TE under serum conditions [13,14]. Compared to the HMW PEI, the LMW PEI illustrates much lower toxicity, yet almost no transfection activity [15]. Recently, plentiful approaches to obtaining high TE using covalently conjugated and non-conveniently assembled LMW PEI have been investigated [16,17]. One of the feasible approaches is to cross-link LMW PEI with biodegradable linkers (ester, ketal and disulfide etc.) [13,18,19] to form “smart” polymers that can eventually degrade into small molecules and simultaneously release complexed nucleic acids in the internal or external stimuli (pH, redox, temperature, light, and magnetic field etc.) [20,21,22,23].
Such endogenous stimuli that are drawing keen attention recently are reactive oxygen species (ROS), which include hydrogen peroxides (H2O2), hydroxyl radicals (·OH), peroxynitrites (ONOO) and superoxides (O2) [24,25,26,27]. Commonly, ROS are generated from mitochondrial electron transport as a byproduct, and they are used in cell signaling of normal cells or cause oxidative stress from overproduction [28]. On the other hand, a number of evidences reveal that chronically increased levels of ROS are closely associated with various pathological disorders including cancer, atherosclerosis, diabetes, infections, inflammatory diseases, where ROS levels can be 10- to 100-times higher than those of the normal levels [29,30,31]. Therefore, ROS can be considered as a target or an indicator for selectively delivering cargo molecules to diseased sites by targeting oxidative microenvironment at different levels. Some materials that can undergo phase transition or hydrolyze under oxidative conditions therefore have been developed to construct ROS-sensitive carriers. Alternatively, some oxidation-labile groups (thioether, thioketal [25,26,32], selenium-containing groups, oligoproline peptide and boronic acid esters etc.) are incorporated into polymers as ROS-responsive groups [33,34,35,36]. It was hypothesized that the ROS-responsive nanocarriers could facilitate the intracellular gene release and transfection expression inspired by the high level of intracellular ROS.
Based on the above issues, the aim of this study was to develop novel biodegradable polymeric nanocarriers based on LWM PEI and thioacetal-linker units, exploiting the high level of ROS in cancer cells (as shown in Scheme 1). In addition, rigid aromatic structure containing polymers showed increased TE was recently reported by our group [37,38,39]. The aromatic rings may help to improve the DNA condensation ability of cationic polymers. Besides, we also found diepoxide ring-opening polymerization is a practical synthetic method toward polymeric vectors with high biological compatibility by the newly formed hydroxyls and oxygen atoms similar to PEG structure [38,39,40,41,42]. Hence, we prepared this series of polycations through the epoxide ring-opening polymerization from bis-epoxides with various aromatic thioacetal groups. Then, their gene delivery properties (such as DNA condensation, cytocompatibility, in vitro TE) and structure-property correlations were systematically investigated.

2. Results and Discussion

2.1. Polymer Synthesis and Characterization

The preparation route for the target polymers is shown in Scheme 2. Various aromatic aldehydes 1 reacted with 2-mercaptoethanol to give compound 2 in the presence of catalyst NiCl2·6H2O. Subsequently, diglycidyl ether 3 was prepared by the reaction of 2 with epichlorohydrin in the presence of NaOH and water with Bu4NBr as a phase transfer catalyst. The ring-opening polymerization was simply processed between equal molar amounts of diglycidyl ethers cross-linker 3 and PEI 600 Da in refluxed ethanol. The crude product was recrystallized for 3 times with anhydrous DCM and methanol to ensure their polydispersity. The obtained polymers showed significant water solubility, which was required for the subsequent studies. Moreover, four diglycidyl ether bridges with varied electron-effects (electron-donating and electron-withdrawing substituents) were introduced for helping us to elucidate the structure–activity relationships (SARs). These new compounds were characterized by 1H-NMR (400 MHz) using D2O as a solvent. Although the molar ratio of the substrates (bridge and PEI 600) for polymerization was 1:1, the integral ratio of the proton signals from the bridge (18H each) and PEI (56H each) revealed that the units of the bridge were more than the latter, indicating the formation of a reticular but not linear structure (Supplementary Materials). The molecular weights of target polymers 4 were measured by GPC, and results in Table 1 showed that the Mws were found to be in the range of 7–10 KDa and the PDIs (polymer dispersity index) were relatively high around 1.3~2. Because it is well-known that the higher molecular weight of polymers always comes with higher cytotoxicity [38], we hope our materials would have lower toxicity while maintaining high TE.

2.2. Polymer Responds to Reactive Oxygen Species

With the polymer 4 in hand, we investigated its response to ROS under simulated conditions. In a typical experiment, polymer 4 was dissolved in D2O containing 100 mM H2O2 to trigger its degradation. When the polymer was incubated at 37 °C for different times, the disappearance of thioketal linkage peak (δ ≈ 5.20 ppm) was monitored by 1H-NMR spectroscopy (Figure S2, Supplementary Materials). The 1H-NMR spectrum confirmed that the thioketal linkages were efficiently cleaved by ROS, generating substituted benzaldehyde (δ ≈ 8.25 ppm) as a byproduct during the cleavage process.

2.3. Interaction with Plasmid DNA and Characterization of Polyplexes

Condensation of negatively charged DNA into nano-sized particles is a prerequisite of great importance for well-designed polymeric vectors. The formation of a polyplex can reduce the electrostatic repulsion between DNA and the cell surface, and can protect DNA against enzymatic degradation by nucleases in cytoplasm or serum [43]. Agarose gel electrophoresis was used to evaluate the DNA binding ability between the polymer and DNA at various weight ratios (polymer/DNA, w/w), and results were shown in Figure 1. All 4 materials exhibited good DNA binding capacity, and full DNA retardation could be observed at a relatively low dosage from the w/w ratio of ~0.5. The structure of aromatic substituent seemed to have little effect on their DNA retardation ability. However, polymers could not efficiently complex with DNA even at a high w/w ratio of 8 after exposed to ROS (Figure S3, Supplementary Materials). This finding implied that polymer 4 was decomposed following incubation with H2O2.
Proper particle size and positive surface charge are essential for efficient gene delivery. It was reported that complexes within the size range of 50 to several hundred nanometers would receive easier endocytosis [44]. Dynamic light scattering (DLS) measurements showed that the particle sizes of 4/DNA polyplexes changed dramatically at relatively low w/w ratios (0.5–1), and became constant at 180~300 nm with the increase of w/w ratio (Figure 2A). The larger particles formed at the w/w ratio of 0.5–1 might be attributed to their neutral zeta-potential, which led to the minimized repulsion and resulting aggregation. Meanwhile, we also examined the possible changes of particle sizes of 4a/DNA at a w/w ratio of 2 in the presence of 10% serum. Results suggested that the particle sizes of polyplexes were still stable at ~250 nm and seldom altered, indicating that no apparent aggregation occurred (Figure S1, Supplementary Materials). Zeta potential shown in Figure 2B indicated the surface charge rose along with the increase of w/w ratios, and reached about +35~50 mV above a w/w ratio of 2. Interestingly, the polyplexes with electron-donating substitute revealed lower zeta potential than the electron-withdrawing ones, which might be due to the positive charge screening by the electron-rich effect. Generally, the positively charged complexes can interact with the negatively charged cellular membranes, leading to more efficient cellular uptake [40].

2.4. In Vitro Gene Transfection

The in vitro TE of the new polyplexes was evaluated in HeLa cells with high ROS levels by using pGL3 plasmid as a luciferase reporter gene. Figure 3A shows the relative TEs at various w/w ratios in a serum-free medium, and Lipofectamine 2000, 25 KDa PEI and PEI 600 were used as controls. All the polymers at w/w ratios of 2 and 4 gave comparable TEs to commercial reagent Lipofectamine 2000. To our delight, polymer 4a gave the highest TE, which was nearly 4.5 times higher TE than Lipofectamine 2000 and 1.5 times higher TE than 25 KDa PEI at a w/w ratio of 2. The electron-withdrawing groups on the aromatic ring seemed to play an important role in the transfection process. We speculate that the lower zeta potentials caused by the electron-rich effect in 4a might benefit the dissociation of the polyplexes, leading to better release of DNA in the cytosol [40].
In general, the interaction between negatively charged serum proteins and polycationic gene vector would inhibit efficient gene delivery [45]. Previous results in DLS experiment showed good serum tolerance of our new material. The transfection ability of the polymers in the presence of serum was also estimated by the same method. As shown in Figure 3B, it was found that the relative TE was even higher for all synthesized polymers in the presence of 10% of serum, indicating that these polyplexes were quite stable and were seldom affected by the serum. Especially 4a polyplexes, demonstrated approximately 10 times higher TE than Lipofectamine 2000 and 9 times higher than 25 KDa PEI, respectively. Besides the aromatic group, the hydroxyls formed from ring-opening polymerization would also contribute to the excellent serum tolerance [38,41].
To directly visualize the infected cells expressing green fluorescent protein reporter gene pEGFP-Nl, enhanced green fluorescent protein expression in HeLa cells was observed by an inverted fluorescent microscope. The w/w ratios were used according to the optimal results from luciferase assays, and the images are shown in Figure 4. Similar to the results in luciferase assay, polymer 4a gave the strongest green fluorescence among the four polymers, and the density of expressed GFP was also higher than that involving control PEI 25 KDa and Lipofectamine 2000. Serum seemed to have no negative effect on the transfection mediated by 4; however, PEI 25 KDa-participated transfection was inhibited by serum on account of high positive charges. All results further demonstrated the good serum tolerance of our new vectors.

2.5. Cytotoxicity

Successful gene transfection requires efficient transfection and minimized cytotoxicity. However, most of the polymeric are caught in the dilemma: either high TE associated with severe cytotoxicity, or low TE with better compatibility [26]. These new polycations have molecular weight around 9 KDa, and previous experiments exhibited that although their molecular weights are relatively low, they could completely condense DNA even at low w/w ratios (~0.5). We hope their small molecular weights may result in low toxicity. The cytotoxicities of the polyplexes were studied and compared with PEI 25 KDa and Lipofectamine 2000 in HeLa cells via CCK-8 assays. It should be noted that the w/w ratio for CCK-8 assay was the same as that used in the transfection experiment. As shown in Figure 5, the cell viabilities of the studied materials were higher than those of 25 KDa PEI and Lipofectamine 2000 even at high w/w ratios in most cases, suggesting that these polymers had better biocompatibility. Comparing to the structure of bPEI, we believe that the lower cytotoxicity may be attributed to the newly formed hydroxyl groups and biodegradable thioacetal, which can benefit the biocompatibility of the polymeric materials used for gene delivery. It was also proved that the ring-opening polymerization from bis-epoxides is an effective synthetic approach toward materials with low cytotoxicity.

3. Experimental Section

3.1. Materials and Methods

Anhydrous MeOH, EtOH and dichloromethane (DCM) were distilled immediately before use after drying and purifying by using standard methods. 2,2′-((4-methoxyphenyl)methylene)bis(sulfanediyl))diethanol (2a), 2,2′-((phenylmethylene)bis(sulfanediyl))diethanol (2b) and 2,2′-((4-fluorophenyl)methylene)bis(sulfanediyl))diethanol (2c) were prepared according to the literature [46]. 0.6 KDa and 25 KDa branched polyethylenimine (PEI) (99%, Sigma-Aldrich, St. Louis, MO, USA), Dulbecco’s Modified Eagle’s Medium (DMEM) and fetal bovine serum (FBS) (Invitrogen Corp., Carlsbad, CA, USA), MicroBCA protein assay kit (Pierce, Appleton, WI, USA), Luciferase assay kit (Promega, Madison, WI, USA), Endotoxin free plasmid purification kit (TIANGEN, Beijing, China) were used as received. Luciferase (pGL-3) and green fluorescent protein (pEGFP-N1) plasmid DNA were purchased from Promega and Clontech. The supercoiled plasmid DNA (pUC-19) used in agarose-gel assay was purchased from Takara (Dalian, China). HeLa cells (human cervix carcinoma cell lines) were purchased from Shanghai Institute of Biochemistry and Cell Biology, Chinese Academy of Sciences. All the other chemicals reagents and solvents of analytical grade, if not specified, were used as received from commercial sources without further purification.
The 1H-NMR spectra were recorded at 400 MHz and 13C spectra at 100 MHz on a Varian INOVA-400 spectrometer (Varian, Palo Alto, CA, USA). The high-resolution mass spectrometry (HRMS) experiments were performed using a Finnigan LCQDECA (Thermo Scientific, Waltham, MA, USA) and a Bruker Daltonics BioTOF mass spectrometer (Bruker Daltonics Inc., Billerica, MA, USA). The Mw and polydispersity index (PDI) of the target polymers were determined by gel permeation chromatography (GPC) system, which consisted of Shodex columns OHPAK KB-803, Waters 515 pump and Waters 2410 Refractive Index Detector. 0.5 mol·L−1 HAc/NaAc buffer was passed through a filter and used as the mobile phase, at a flow rate of 0.5 mL·min−1. Mws were calculated against PEG standards of Mn ranging from 900 to 80,000.

3.2. Synthesis of Title Polymers

3.2.1. Preparation of 2,2′-((4-(Trifluoromethyl)phenyl)methylene)bis(sulfanediyl))diethanol (Compound 2d)

4-(Trifluoromethyl)benzaldehyde (1d, 20 mmol, 3.48 g) was mixed with 2-mercaptoethanol (40 mmol, 3.12 g). After addition of the catalyst NiCl2·6H2O (0.1 mmol, 23.8 mg), the solution was stirred at room temperature for 1 h, and then 10 mL DCM was added to separate out the catalyst by filtering off. The solvent was concentrated to afford a white solid, which was purified by column chromatography on a silica gel (DCM:MeOH = 40:1, v/v) to give compound 2d as a white solid. Yield: 77.6%. 1H-NMR (400 MHz, CDCl3) δ (ppm) 7.69–7.48 (m, 4H, PhH), 5.18 (s, 1H, -SCHS-), 3.78 (t, J = 5.8 Hz, 4H, -CH2OH), 2.96–2.66 (m, 4H, -CH2CH2OH). 13C-NMR (100 MHz, CDCl3) δ (ppm) 144.16, 128.10, 125.77, 125.73, 125.70, 125.66, 61.57, 52.57, 35.32. HRMS (ESI): m/z calcd. for C12H15F3O2S2 (M+) 312.0466; found = 335.0358 ([M + Na]+, 100).

3.2.2. Preparation of Diglycidyl Ether Linkers 3

Compounds 3 were obtained using the method previously reported [37,40]. Briefly, compound 2 (0.02 mol), epichlorohydrin (4.67 mL, 0.06 mol), NaOH (2.4 g, 0.06 mol), tetrabutylammonium chloride (0.3224 g, 0.001 mol) and pure water (1 mL, 0.056 mol) were mixed at room temperature and stirred at 35 °C overnight. The solid residue was separated out by filtering off and washed with DCM. The combined solvent was concentrated, and the residue was purified by a silica gel column chromatography to give the compound 3. Analytical data for new compounds 3ad were:
3a: white solid, yield: 31.2%. Eluent: PE/EA = 3:1 (v/v). 1H-NMR (400 MHz, CDCl3): δ (ppm) 7.39–6.84 (m, 4H, PhH), 5.12 (s, 1H, -SCHS-), 3.81–3.78 (m, 3H, -OCH3), 3.76–3.33 (m, 8H, -CH2OCH2-), 3.13 (m, 2H, ring CH), 2.85–2.77 (m, 4H, -SCH2), 2.73–2.59 (m, 4H, ring CH2). 13C-NMR (100 MHz, CDCl3): δ (ppm) 159.18, 132.14, 128.92, 113.84, 71.50, 70.96, 55.25, 53.26, 50.72, 44.11, 31.73. HRMS (ESI): m/z calcd. for C18H26O5S2 (M+) 386.1222; found = 409.1117 ([M + Na]+, 100).
3b: white solid, yield: 33.6%. Eluent: PE/EA = 3:1 (v/v). 1H-NMR (400 MHz, CDCl3): δ (ppm) 7.45–7.25 (m, 4H, PhH), 5.12 (s, 1H, -SCHS-), 3.76–3.35 (m, 8H, -CH2OCH2-), 3.14–3.12 (m, 2H, ring CH), 2.85–2.78 (m, 4H, -SCH2), 2.75–2.60 (m, 4H, ring CH2). 13C-NMR (100 MHz, CDCl3): δ (ppm) 140.20, 128.55, 127.97, 127.73, 71.52, 70.96, 70.93, 53.84, 50.74, 44.15, 31.74. HRMS (ESI): m/z calcd. for C17H24O4S2 (M+) 356.1116; found = 379.1010 ([M + Na]+, 100).
3c: pale-yellow oil, yield: 28.6%. Eluent: PE/EA = 2:1 (v/v). 1H-NMR (400 MHz, CDCl3): δ (ppm) 7.50–7.00 (m, 4H, PhH), 5.17 (s, 1H, -SCHS-), 3.79–3.33 (m, 8H, -CH2OCH2-), 3.19–3.10 (m, 2H, ring CH), 2.90–2.76 (m, 4H, -SCH2), 2.74–2.61 (m, 4H, ring CH2). 13C-NMR (100 MHz, CDCl3): δ (ppm) 163.39, 160.94, 136.16, 136.13, 129.52, 129.44, 115.50, 115.29, 71.56, 71.02, 53.08, 50.74, 50.73,44.09, 31.82, 30.90. HRMS (ESI): m/z calcd. for C17H23FO4S2 (M+) 374.1022; found = 397.0919 ([M + Na]+, 100).
3d: pale-yellow oil, yield: 21.3%. Eluent: PE/EA = 2:1 (v/v). 1H-NMR (400 MHz, CDCl3): δ (ppm) 7.62–7.57 (m, 4H, PhH), 5.24 (s, 1H, -SCHS-), 3.82–3.29 (m, 8H, -CH2OCH2-), 3.17–3.10 (m, 2H, ring CH), 2.89–2.77 (m, 4H, -SCH2), 2.74–2.57 (m, 4H, ring CH2). 13C-NMR (100 MHz, CDCl3): δ (ppm) 144.52, 128.31, 128.20, 125.57, 125.53, 73.41, 72.45, 72.44, 72.20, 71.62, 71.08, 71.06, 69.51, 53.30, 50.77, 50.76, 45.78, 44.09, 31.88, 30.86. HRMS (ESI): m/z calcd. for C18H23F3O4S2 (M+) 424.0990; found = 447.0890 ([M + Na]+, 100).

3.2.3. Synthesis and Characterization of Target Polymers 4

In a typical polymerization procedure, PEI 600 Da (0.5 mmol) and diglycidyl ether linkers 3 (0.5 mmol) were dissolved with 1 mL of anhydrous EtOH in a container. Under the protection of nitrogen (N2), the reaction mixture was stirred at 80 °C for 72 h. The resulting crude product was recrystallized from anhydrous DCM/methanol (v/v = 1/1). The recrystallized oily precipitate was isolated and dried until a constant weight was achieved. The molecular weights of compounds 4 were measured by GPC.
4a: Yield: 35.6%. 1H-NMR (400 MHz, D2O): δ (ppm) 7.55–6.80 (m, 4H, PhH), 5.18 (s, 1H, -SCHS-), 3.98–2.20 (m, 33H, -SCH2CH2O-, -OCH2CH(OH)CH2-, -NHCH2CH2-). GPC: Mw = 9871, PDI = 1.85.
4b: Yield: 37.1%. 1H-NMR (400 MHz, D2O): δ (ppm) 7.63–7.00 (m, 5H, PhH), 5.17 (s, 1H, -SCHS-), 4.08–1.94 (m, 42H, -SCH2CH2O-, -OCH2CH(OH)CH2-, -NHCH2CH2-). GPC: Mw = 10,916, PDI = 1.97.
4b: Yield: 29.8%. 1H-NMR (400 MHz, D2O): δ (ppm) 7.45–6.64 (m, 4H, PhH), 5.13 (s, 1H, -SCHS-), 4.11–2.01 (m, 35H, -SCH2CH2O-, -OCH2CH(OH)CH2-, -NHCH2CH2-). GPC: Mw = 7123, PDI = 1.70.
4b: Yield: 31.2%. 1H-NMR (400 MHz, D2O): δ (ppm) 7.77–7.18 (m, 4H, PhH), 5.21 (s, 1H, -SCHS-), 4.02–2.05 (m, 38H, -SCH2CH2O-, -OCH2CH(OH)CH2-, -NHCH2CH2-). GPC: Mw = 8209 PDI = 1.40.

3.3. Reactive Oxygen Species-Triggered Degradation of Thioketal Linkages

The degradation of thioketal linkages in polymer 4 under ROS conditions was investigated by incubating 4 (5 mg) with 100 mM of H2O2 in 0.6 mL of D2O at 37 °C for various periods of time. The disappearance of the thioketal linkage peak (δ ~ 5.20 ppm) was analyzed by using 1H-NMR.

3.4. Agarose Gel Retardation

pUC-19 (5 μL of 0.025 mg/mL in H2O) was mixed with the required amount of polymer to obtain the varied w/w ratios in H2O (a total volume of 10 μL). After an incubation time of 30 min at 37 °C, the polyplex solution was loaded onto an agarose gel (0.7% w/v agarose gel containing GelRedTM) and electrophoresed at 120 V for 40 min. A Vilber Lourmat imaging system was utilized to image the agarose gels [36].
To investigate the polymer stability under ROS conditions, the polymer solution (1 mg/mL) was treated with 100 mM H2O2 for 48 h at 37 °C. Subsequently, 0.125 μg pUC-19 and the desired amount of polymers at vary w/w ratios were mixed in 10 μL of DI for 0.5 h. The samples were run at the same electrophoresis condition as described above.

3.5. Particle Size and Zeta Potential Measurements

A Malvern Instruments Zetasizer Nano-ZS (ZEN3600, Malvern Instruments Ltd., Worcestershire, UK) was used to measure the complexes size and zeta potential. Polymer/DNA complexes were prepared at varying w/w ratios as described above. Samples were then diluted up to 1 mL using purity water before being measured [36]. In the experiments with serum, FBS (10% final concentrations) was added to the formulated polyplexes and mixed for 30 s. The particle sizes of the polyplexes were determined using Dynamic light scattering (DLS). Data were shown as mean ± standard deviation (S.D.) based on three independent measurements.

3.6. Reactive Oxygen Species-Responsive of Polyplexes

The ROS-responsive tests were conducted by mixing the complexes (4a/DNA at w/w of 2) with 100 μM H2O2 (final concentrations) at 37 °C for 1 days. After 12 and 24 h, the polyplexes were measured through DLS to obtain particle sizes and size distributions.

3.7. In Vitro Transfection Experiments

Gene transfection of a series of complexes was investigated in HeLa cells using two different plasmids encoding for green fluorescence protein (pEGFP-N1) and luciferase (pGL-3). Cells were seeded at a density of 7 × 104 cells per well in 24-well plates and incubated for 24 h to achieve ~70–80% confluency. The culture medium was replaced with FBS free or 10% FBS containing DMEM medium before transfection. Polymer/DNA (1 μg) complexes were added to each well and incubated at 37 °C. Control reagents 25 KDa PEI (at a w/w ratio of 1.4, N/P = 10) [4,14,17] and Lipofectamine 2000 were formulated with DNA based upon their recommended protocols. After 4 h of incubation, the transfection medium was replaced with fresh complete medium containing 10% FBS and further incubated for 20 h. The images of GFP expressed cells were taken with an inverted fluorescence microscope (Nikon Eclipse TE 2000E, Nikon, Tokyo, Japan).
For the luciferase expression, cells were washed twice with PBS (pH 7.4) and lysed using 100 μL 1× Lysis reporter buffer. The luciferase activity was quantified using the luciferase assay reagent (Promega). The total protein content of the cell lysate was analyzed by BCA protein assay. The gene TE was expressed as the relative fluorescence intensity per mg protein (RLU/mg protein). All transfection experiments were performed as replicates of three [17].

3.8. Cytotoxicity Assay

The cytotoxicity studies were performed using Cell Counting Kit-8 (CCK-8) assay. HeLa cells were seeded in 96-well plates at a density of 8000 cells per well and allowed to adhere for 24 h. Complexes prepared at varied w/w ratios (2, 4, 6 corresponding to final concentrations were 4, 8, 12 μg/mL) were added to the FBS free growth medium and left to incubated for 4 h. Following incubation, the wells were replaced with fresh complete medium and incubated for a further 24 h. Subsequently, 10 μL of CCK-8 was then added to each well and the cells were incubated for 1 h at 37 °C. After that, the aborbance was readed using enzyme-linked immunosorbent assay (ELISA) plate reader (Model 680, Bio-Rad, Hercules, CA, USA) at a wavelength of 490 nm. The relative cell viability (%) related to untreated control cells was calculated by test/control × 100 [42]. Values were given as mean of triplicates ± S.D.

3.9. Statistical Analysis

Results are summarized as mean ± S.D., and statistical significance of differences was evaluated by variance analysis (ANOVA): p values smaller than 0.05 were considered to be significant [39].

4. Conclusions

In summary, we have successfully synthesized a series of ROS-responsive materials by the ring-opening polymerization between PEI 600 and diepoxide containing stimuli-responsive thioacetal groups. Four diglycidyl ethers with various electron-effects were employed in the side chain structure to facilitate the study of the SAR. These materials could efficiently condense DNA into stable nanoparticles with proper sizes and zeta-potentials. Besides, the thioketal linkages in polymers could also be dissociated under ROS-rich conditions for efficient gene delivery. Compared with 25 KDa PEI and Lipofectamine 2000, these polymers showed much higher TE in HeLa cells, especially polymer 4a with electron-withdrawing substituent on the aromatic ring. More importantly, unlike PEI, serum had little negative effect on the transfection by these materials, and their TEs were even increased with the presence of 10% serum. The better serum tolerance of the polymers might come from their evenly distributed hydroxyl groups. Moreover, the cationic polymers exhibited good cell viabilities. The collective data suggested such polymer could be a promising target nanocarrier exploiting the high levels of intracellular ROS in cancer cells. Further modifications of the polymer structure and in-depth mechanism studies are now in progress.

Supplementary Materials

The following are available online. Figure S1–S3 and Table S1. Additionally, 1H, 19F and 13C-NMR and GPC data for the compounds are provided.

Author Contributions

W.-J.Y. and Q.L. conceived and designed the experiments; G.-Q.L. performed the experiments; W.-J.Y. wrote the paper; Z.-G.Z. and X.-J.Y. provide the resources.

Funding

This work was financially supported by the National Science Foundation of China (No. 2170021243), the Science and Technology Department of Sichuan Province (No. 2015JY0115), and the Fundamental Research Funds for the Central Universities, Southwest Minzu University (No. 2018HQZZ19).

Acknowledgments

Wen-Jing Yi thanks Xiao-Qi Yu and Ji Zhang from the Key Laboratory of Green Chemistry and Technology (Ministry of Education), College of Chemistry, Sichuan University for their support.

Conflicts of Interest

The authors declare there is no conflicts of interest regarding the publication of this paper.

References

  1. Cho, H.; Cho, Y.-W.; Kang, S.-W.; Kwak, M.-K.; Huh, K.M.; Bae, Y.H.; Kang, H.C. Tempo-spatial activation of sequential quadruple stimuli for high gene expression of polymeric gene nanocomplexes. Mol. Pharm. 2017, 14, 842–855. [Google Scholar] [CrossRef] [PubMed]
  2. Ilarduya, C.T.D.; Sun, Y.; Düzgüneş, N. Gene delivery by lipoplexes and polyplexes. Eur. J. Pharm. Sci. 2010, 40, 159–170. [Google Scholar] [CrossRef] [PubMed]
  3. Mintzer, M.A.; Simanek, E.E. Nonviral vectors for gene delivery. Chem. Rev. 2009, 109, 259–302. [Google Scholar] [CrossRef] [PubMed]
  4. Xu, C.-T.; Chen, G.; Nie, X.; Wang, L.-H.; Ding, S.-G.; You, Y.-Z. Low generation PAMAM-based nanomicelles as ROS-responsive gene vectors with enhanced transfection efficacy and reduced cytotoxicity in vitro. New J. Chem. 2017, 41, 3273–3279. [Google Scholar] [CrossRef]
  5. Bouard, D.; Alazard-Dany, N.; Cosset, F.L. Viral vectors: From virology to transgene expression. Br. J. Pharmacol. 2009, 157, 153–165. [Google Scholar] [CrossRef] [PubMed]
  6. Guan, Y.; Lu, H.; Li, W.; Zheng, Y.; Jiang, Z.; Zou, J.; Gao, H. Near-infrared triggered upconversion polymeric nanoparticles based on aggregation-induced emission and mitochondria targeting for photodynamic cancer therapy. ACS Appl. Mater. Interfaces 2017, 9, 26731–26739. [Google Scholar] [CrossRef] [PubMed]
  7. Chen, W.; Deng, W.; Goldys, E.M. Light-triggerable liposomes for enhanced endolysosomal escape and gene silencing in PC12 cells. Mol. Ther. Nucleic Acids 2017, 7, 366–377. [Google Scholar] [CrossRef] [PubMed]
  8. Lee, D.-J.; He, D.; Kessel, E.; Padari, K.; Kempter, S.; Lächelt, U.; Rädler, J.O.; Pooga, M.; Wagner, E. Tumoral gene silencing by receptor-targeted combinatorial siRNA polyplexes. J. Control. Release 2016, 244 Pt B, 280–291. [Google Scholar] [CrossRef]
  9. Truong, N.P.; Gu, W.; Prasadam, I.; Jia, Z.; Crawford, R.; Xiao, Y.; Monteiro, M.J. An influenza virus-inspired polymer system for the timed release of siRNA. Nat. Commun. 2013, 4, 1902. [Google Scholar] [CrossRef] [PubMed]
  10. Hartono, S.B.; Phuoc, N.T.; Yu, M.; Jia, Z.; Monteiro, M.J.; Qiao, S.; Yu, C. Functionalized large pore mesoporous silica nanoparticles for gene delivery featuring controlled release and co-delivery. J. Mater. Chem. B 2014, 2, 718–726. [Google Scholar] [CrossRef]
  11. Rosariomeléndez, R.; Yu, W.; Uhrich, K.E. Biodegradable polyesters containing ibuprofen and naproxen as pendant groups. Biomacromolecules 2013, 14, 3542–3548. [Google Scholar] [CrossRef] [PubMed]
  12. Neu, M.; Fischer, D.; Kissel, T.J. Recent advances in rational gene transfer vector design based on poly(ethylene imine) and its derivatives. J. Gene Med. 2005, 7, 992–1009. [Google Scholar] [CrossRef] [PubMed]
  13. Xun, M.-M.; Zhang, J.-H.; Liu, Y.-H.; Zhang, J.; Xiao, Y.-P.; Guo, Q.; Li, S.; Yu, X.-Q. Polyethylenimine analogs for improved gene delivery: Effect of the type of amino groups. RSC Adv. 2016, 6, 5391–5400. [Google Scholar] [CrossRef]
  14. Li, H.; Jiang, H.; Zhao, M.; Fu, Y.; Sun, X. Intracellular redox potential-responsive micelles based on polyethylenimine-cystamine-poly(ε-caprolactone) block copolymer for enhanced miR-34a delivery. Polym. Chem. 2015, 6, 1952–1960. [Google Scholar] [CrossRef]
  15. Sarkar, K.; Debnath, M.; Kundu, P.P. Preparation of low toxic fluorescent chitosan-graft-polyethyleneimine copolymer for gene carrier. Carbohydr. Polym. 2013, 92, 2048–2057. [Google Scholar] [CrossRef] [PubMed]
  16. Yoshitomi, T.; Hirayama, A.; Nagasaki, Y. The ROS scavenging and renal protective effects of pH-responsive nitroxide radical-containing nanoparticles. Biomaterials 2011, 32, 8021–8028. [Google Scholar] [CrossRef] [PubMed]
  17. Xun, M.-M.; Xiao, Y.-P.; Zhang, J.; Liu, Y.-H.; Peng, Q.; Guo, Q.; Wu, W.-X.; Xu, Y.; Yu, X.-Q. Low molecular weight PEI-based polycationic gene vectors via Michael addition polymerization with improved serum-tolerance. Polymer 2015, 65, 45–54. [Google Scholar] [CrossRef]
  18. Mao, C.Q.; Du, J.Z.; Sun, T.M.; Yao, Y.D.; Zhang, P.Z.; Song, E.W.; Wang, J. A biodegradable amphiphilic and cationic triblock copolymer for the delivery of siRNA targeting the acid ceramidase gene for cancer therapy. Biomaterials 2011, 32, 3124–3133. [Google Scholar] [CrossRef] [PubMed]
  19. Liu, S.; Huang, W.; Jin, M.-J.; Fan, B.; Xia, G.-M.; Gao, Z.-G. Inhibition of murine breast cancer growth and metastasis by survivin-targeted siRNA using disulfide cross-linked linear PEI. Eur. J. Pharm. Sci. 2016, 82, 171–182. [Google Scholar] [CrossRef] [PubMed]
  20. Yuan, Y.; Zhang, C.J.; Liu, B. A photoactivatable AIE polymer for light-controlled gene delivery: Concurrent endo/lysosomal escape and DNA unpacking. Angew. Chem. Int. Ed. 2015, 54, 1–6. [Google Scholar] [CrossRef] [PubMed]
  21. Kim, J.; Lee, Y.M.; Kim, H.; Park, D.; Kim, J.; Kim, W.J. Phenylboronic acid-sugar grafted polymer architecture as a dual stimuli-responsive gene carrier for targeted anti-angiogenic tumor therapy. Biomaterials 2016, 75, 102–111. [Google Scholar] [CrossRef] [PubMed]
  22. Ganta, S.; Devalapally, H.; Shahiwala, A.; Amiji, M. A review of stimuli-responsive nanocarriers for drug and gene delivery. J. Control. Release 2008, 126, 187–204. [Google Scholar] [CrossRef] [PubMed]
  23. Fleige, E.; Quadir, M.A.; Haag, R. Stimuli-responsive polymeric nanocarriers for the controlled transport of active compounds: Concepts and applications. Adv. Drug Deliv. Rev. 2012, 64, 866–884. [Google Scholar] [CrossRef] [PubMed]
  24. Li, Y.; Gao, J.; Zhang, C.; Cao, Z.; Cheng, D.; Liu, J.; Shuai, X. Stimuli-responsive polymeric nanocarriers for efficient gene delivery. Top. Curr. Chem. 2017, 375, 27. [Google Scholar] [CrossRef] [PubMed]
  25. Liu, X.; Wang, Y.; Chen, C.; Tintaru, A.; Cao, Y.; Liu, J.; Ziarelli, F.; Tang, J.; Guo, H.; Rosas, R.; et al. A fluorinated bola-amphiphilic dendrimer for on-demand delivery of siRNA, via specific response to reactive oxygen species. Adv. Funct. Mater. 2016, 26, 8594–8603. [Google Scholar] [CrossRef]
  26. Shim, M.S.; Xia, Y. A reactive oxygen species (ROS)-responsive polymer for safe, efficient, and targeted gene delivery in cancer cells. Angew. Chem. Int. Ed. 2013, 52, 6926–6929. [Google Scholar] [CrossRef] [PubMed]
  27. He, X.; Chen, X.; Liu, L.; Zhang, Y.; Lu, Y.; Zhang, Y.; Chen, Q.; Ruan, C.; Guo, Q.; Li, C.; et al. Sequentially triggered nanoparticles with tumor penetration and intelligent drug release for pancreatic cancer therapy. Adv. Sci. 2018, 5, 1701070. [Google Scholar] [CrossRef] [PubMed]
  28. Yoo, J.; Rejinold, N.S.; Lee, D.; Jon, S.; Kim, Y.C. Protease-activatable cell-penetrating peptide possessing ROS-triggered phase transition for enhanced cancer therapy. J. Control. Release 2017, 264, 89–101. [Google Scholar] [CrossRef] [PubMed]
  29. Zhang, Q.; Zhang, F.; Chen, Y.; Dou, Y.; Tao, H.; Zhang, D.; Wang, R.; Li, X.; Zhang, J. Structure-property correlations of reactive oxygen species-responsive and hydrogen peroxide-eliminating materials with anti-oxidant and anti-inflammatory activities. Chem. Mater. 2017, 29, 8221–8238. [Google Scholar] [CrossRef]
  30. Lee, S.H.; Boire, T.C.; Lee, J.B.; Gupta, M.K.; Zachman, A.L.; Rath, R.; Sung, H.J. ROS-cleavable proline oligomer crosslinking of polycaprolactone for pro-angiogenic host response. J. Mater. Chem. B 2014, 2, 7109–7113. [Google Scholar] [CrossRef] [PubMed]
  31. Yu, L.-Y.; Su, G.-M.; Chen, C.-K.; Chiang, Y.-T.; Lo, C.-L. Specific cancer cytosolic drug delivery triggered by oxygen species-responsive micelles. Biomacromolecules 2016, 17, 3040–3047. [Google Scholar] [CrossRef] [PubMed]
  32. Wilson, D.S.; Dalmasso, G.; Wang, L.; Sitaraman, S.V.; Merlin, D.; Murthy, N. Orally delivered thioketal nanoparticles loaded with TNF-α–siRNA target inflammation and inhibit gene expression in the intestines. Nat. Mater. 2010, 9, 923–928. [Google Scholar] [CrossRef] [PubMed]
  33. Song, C.-C.; Du, F.-S.; Li, Z.-C. Oxidation-responsive polymers for biomedical applications. J. Mater. Chem. B 2014, 2, 3413–3426. [Google Scholar] [CrossRef]
  34. Cheng, R.; Meng, F.; Deng, C.; Zhong, Z. Bioresponsive polymeric nanotherapeutics for targeted cancer chemotherapy. Nano Today 2015, 10, 656–670. [Google Scholar] [CrossRef]
  35. Saravanakumar, G.; Kim, J.; Kim, W.J. Reactive-oxygen-species-responsive drug delivery systems: Promises and challenges. Adv. Sci. 2017, 4, 1600124. [Google Scholar] [CrossRef] [PubMed]
  36. Luo, C.Q.; Xing, L.; Cui, P.F.; Qiao, J.B.; He, Y.J.; Chen, B.A.; Jin, L.; Jiang, H.L. Curcumin-coordinated nanoparticles with improved stability for reactive oxygen species-responsive drug delivery in lung cancer therapy. Int. J. Nanomed. 2017, 12, 855–869. [Google Scholar] [CrossRef] [PubMed]
  37. Yi, W.-J.; Yu, X.-C.; Wang, B.; Zhang, J.; Yu, Q.-Y.; Zhou, X.-D.; Yu, X.-Q. TACN-based oligomers with aromatic backbones for efficient nucleic acid delivery. Chem. Commun. 2014, 50, 6454–6457. [Google Scholar] [CrossRef] [PubMed]
  38. Luan, C.-R.; Liu, Y.-H.; Zhang, J.; Yu, Q.-Y.; Huang, Z.; Wang, B.; Yu, X.-Q. Low molecular weight oligomers with aromatic backbone as efficient nonviral gene vectors. ACS Appl. Mater. Interfaces 2016, 8, 10743–10751. [Google Scholar] [CrossRef] [PubMed]
  39. Liu, Q.; Su, R.-C.; Yi, W.-J.; Zhao, Z.-G. Biodegradable poly(amino ester) with aromatic backbone as efficient nonviral gene delivery vectors. Molecules 2017, 22, 566. [Google Scholar] [CrossRef] [PubMed]
  40. Yi, W.-J.; Zhang, Q.-F.; Zhang, J.; Liu, Q.; Ren, L.; Chen, Q.-M.; Guo, L.; Yu, X.-Q. Cyclen-based lepidic oligomers as potential gene delivery vehicles. Acta Biomater. 2014, 10, 1412–1422. [Google Scholar] [CrossRef] [PubMed]
  41. Zhang, Q.-F.; Yu, Q.-Y.; Geng, Y.; Zhang, J.; Wu, W.-X.; Wang, G.; Gu, Z.; Yu, X.-Q. Ring-opening polymerization for hyperbranched polycationic gene delivery vectors with excellent serum tolerance. ACS Appl. Mater. Interfaces 2014, 6, 15733–15742. [Google Scholar] [CrossRef] [PubMed]
  42. Guo, Q.; Liu, Y.-H.; Xun, M.-M.; Zhang, J.; Huang, Z.; Zhou, X.-D.; Yu, X.-Q. Diol glycidyl ether-bridged low molecular weight PEI as potential gene delivery vehicles. J. Mater. Chem. B 2015, 3, 2660–2670. [Google Scholar] [CrossRef]
  43. Yudovin-Farber, I.; Domb, A.J. Cationic Polysaccharides for Gene Delivery. Mater. Sci. Eng. C 2007, 27, 595–598. [Google Scholar] [CrossRef]
  44. Liu, Y.M.; Reineke, T.M. Hydroxyl stereochemistry and amine number within Poly(glycoamidoamine)s affect intracellular DNA delivery. J. Am. Chem. Soc. 2005, 127, 3004–3015. [Google Scholar] [CrossRef] [PubMed]
  45. He, Y.; Cheng, G.; Xie, L.; Nie, Y.; He, B.; Gu, Z. Polyethyleneimine/DNA polyplexes with reduction-sensitive hyaluronic acid derivatives shielding for targeted gene delivery. Biomaterials 2013, 34, 1235–1245. [Google Scholar] [CrossRef] [PubMed]
  46. Laskar, R.A.; Begum, N.A.; Mir, M.H.; Rohman, M.R.; Khan, A.T. Nickel(II) chloride hexahydrate catalyzed reaction of aromatic aldehydes with 2-mercaptoethanol: Formation of supramolecular helical assemblage of the product. Tetrahedron Lett. 2013, 54, 5839–5844. [Google Scholar] [CrossRef]
  • Sample Availability: Not available.
Scheme 1. Illustration of intracellular delivery of plasmid DNA to the nucleus of HeLa cancer cell using ROS-responsive polymer based LWM PEI and thioacetal-linker units.
Scheme 1. Illustration of intracellular delivery of plasmid DNA to the nucleus of HeLa cancer cell using ROS-responsive polymer based LWM PEI and thioacetal-linker units.
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Scheme 2. Synthetic route of the target polymers. (i) NiCl2·6H2O, rt. (ii) epichlorohydrin, Bu4NBr, NaOH, NaOH, H2O, 35 °C. (iii) EtOH, reflux.
Scheme 2. Synthetic route of the target polymers. (i) NiCl2·6H2O, rt. (ii) epichlorohydrin, Bu4NBr, NaOH, NaOH, H2O, 35 °C. (iii) EtOH, reflux.
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Figure 1. Agarose gel electrophoresis assays of polymer/DNA (pUC19) complexes at different w/w ratios. In each image, the first lane is the DNA control.
Figure 1. Agarose gel electrophoresis assays of polymer/DNA (pUC19) complexes at different w/w ratios. In each image, the first lane is the DNA control.
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Figure 2. Particle size (A) and zeta-potential (B) of polymer/DNA polyplexes obtained at various w/w ratios by DLS. Data are represented by mean ± standard deviation (S.D.) (n = 3).
Figure 2. Particle size (A) and zeta-potential (B) of polymer/DNA polyplexes obtained at various w/w ratios by DLS. Data are represented by mean ± standard deviation (S.D.) (n = 3).
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Figure 3. Luciferase gene expression transfected by polyplexes at different weight ratios: 2, 4, and 6 in comparison with Lipofectamine 2000, PEI 600 (w/w = 6, N/P = 28.7) and 25 KDa PEI (w/w = 1.4, N/P = 10) in human human cervix carcinoma cell lines (HeLa) in the absence of serum (A) and in the presence of 10% serum (B). Data are represented by mean ± S.D. (n = 3).
Figure 3. Luciferase gene expression transfected by polyplexes at different weight ratios: 2, 4, and 6 in comparison with Lipofectamine 2000, PEI 600 (w/w = 6, N/P = 28.7) and 25 KDa PEI (w/w = 1.4, N/P = 10) in human human cervix carcinoma cell lines (HeLa) in the absence of serum (A) and in the presence of 10% serum (B). Data are represented by mean ± S.D. (n = 3).
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Figure 4. Fluorescence microscope image of pEGFP-transfected HeLa cells at optimal weight ratios in the absence of serum (2 for 4ad) or in the presence of 10% FBS (4 for 4a and 4d, 2 for 4b and 4c).
Figure 4. Fluorescence microscope image of pEGFP-transfected HeLa cells at optimal weight ratios in the absence of serum (2 for 4ad) or in the presence of 10% FBS (4 for 4a and 4d, 2 for 4b and 4c).
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Figure 5. Cytotoxicity of polyplexes at different w/w ratios toward HeLa cells. Lipofectamine 2000 and PEI 25 KDa were used as controls (w/w = 1.4, N/P = 10). Data are represented by mean ± S.D. (n = 3).
Figure 5. Cytotoxicity of polyplexes at different w/w ratios toward HeLa cells. Lipofectamine 2000 and PEI 25 KDa were used as controls (w/w = 1.4, N/P = 10). Data are represented by mean ± S.D. (n = 3).
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Table 1. Molecular weights and polydispersities of the target polymers.
Table 1. Molecular weights and polydispersities of the target polymers.
PolymersMw (Da)PDI
4a98711.85
4b10,9161.97
4c71231.70
4d82091.40

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