Galactosamine-Conjugating Zwitterionic Block Copolymer for Reduction-Responsive Release and Active Targeted Delivery of Doxorubicin to Hepatic Carcinoma Cells

Zhai, Jingming; Zhou, Biyu; An, Yanhui; Lu, Binzhong; Fan, Yonggang; Li, Junbo

doi:https://doi.org/10.1155/2020/7863709

Journal of Nanomaterials

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Abstract Introduction Materials and Methods Results and Discussion Conclusions Data Availability Conflicts of Interest Acknowledgments References Copyright Related Articles

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Advanced Nano/Micro Materials for Drug Delivery Applications

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Research Article | Open Access

Volume 2020 | Article ID 7863709 | https://doi.org/10.1155/2020/7863709

Galactosamine-Conjugating Zwitterionic Block Copolymer for Reduction-Responsive Release and Active Targeted Delivery of Doxorubicin to Hepatic Carcinoma Cells

Jingming Zhai,¹Biyu Zhou,²Yanhui An,¹Binzhong Lu,²Yonggang Fan,¹and Junbo Li^1,2

Guest Editor: Anuj Kumar

Received16 Jan 2020

Accepted04 Mar 2020

Published20 Apr 2020

Abstract

Nanocarriers with integrated advantage, such as excellent stealth property, active targeting function, and rapid intracellular drug release, are significant for cancer treatment. Herein, a biodegradable zwitterionic triblock copolymer containing disulfide-linked poly-ε-caprolactone and polycarboxybetaine methacrylate (PCB-SS-PCL-SS-PCB) was first synthesized and then partly modified with galactosamine (GAL) for constructing polymeric micelle drug carrier with multifunctionality. Polymeric micelles showed ultralow protein absorption in serum and obvious reduction-responsiveness in the presence of glutathione, provided by the zwitterionic polymer shell and the disulfide bond, respectively. Furthermore, active targeting of the carrier to hepatic carcinoma cells was achieved via GAL ligands on PCB shells due to their specific binding to asialoglycoprotein receptors on the cell surface. As expected, in vivo competition studies demonstrated that doxorubicin- (DOX-) loaded GAL-modified micelles have better anticancer effect in hepatic tumor-bearing mice than free DOX and nontargetable micelles. As a result, this novel multifunctional carrier provides a valuable strategy to design promising anticancer drug delivery systems for liver cancer treatment.

1. Introduction

Chemotherapeutics are still the main treatment strategy for human cancer [1]. To reduce side effects and enhance bioavailability of hydrophobic drugs, nanodrug delivery systems (NDDS) have been widely explored in cancer chemotherapeutics during past decades [2, 3]. Generally, therapeutic nanoparticles required a hydrophilic coating to ensure a stealthy and long circulation in the bloodstream [4]. To date, polyethylene glycol (PEG) is the most widely used biointerface materials to prevent nonspecific protein adhesion on nanoparticles [5, 6], resulting in a passive accumulation of cargo in the tumor site via a so-called enhanced permeability and retention (EPR) effect [7, 8]. However, recent reports revealed that anti-PEG immunoglobulin antibodies detected in PEGylated systems after repeated administration lead to an insufficient antitumor efficacy caused by an accelerated blood clearance (ABC) phenomenon [9, 10].

Zwitterionic polymers are also neutral and ultrahydrophilic since they bear an equimolar number opposite ionizable group in monomeric unit [1]. The unique structure enables a zwitterionic layer to tightly bind water molecules via ion interaction, giving rise in ultrahigh resistance to protein adsorption and excellent blood compatibility. Moreover, without detectable immune response and avoiding ABC phenomenon, zwitterionic polymers have been also identified as better biointerface material alternative PEG [11, 12]. Recently, a variety of zwitterionic therapeutic nanoparticles, such as polymer-drug conjugates [13], nanogels [14], and polymeric micelles [15] have been developed. However, overcoming their less efficient tumor cell uptake is still a challenge [16].

Among zwitterionic polymers, such as polyphosphobetaine and polysulfobetaine, polycarboxybetaine (PCB) has superior abilities because of its reactive carboxylate anion, which can readily conjugate with amine-containing biomolecules via simple carbodiimide chemistry [17]. Although the modification has little influence on the antifouling property, it introduces novel functions [18–20]. For instance, to address the reduced cell uptake efficacy of zwitterionic nanoparticles, Lin et al. used c(RGDyK)-modified PCB to obtain micelle carriers with prolonged blood circulation time and active targeting property to improve therapeutic efficacy in vivo [21]. Furthermore, based on the specific recognition of asialoglycoprotein (ASGP) receptors to glycoproteins on hepatic carcinoma cells [22, 23], the immobilization of galactosamine on PCB substrates allows the adhesion-based selection of hepatocytes differing from other cell types [24]. Jiang’s group also used fluorescein and galactose with the amine group to modify PLGA-PCB nanoparticles for selectively binding HepG2 cells [25]. The modification of galactose ligand on zwitterionic nanoparticles has exhibited an integrated ultrahigh antifouling and tumor-targeting properties to hepatic carcinoma cells. However, the in vivo antitumor effect of such NDDS needs further invistigation.

In addition to long circulation and tumor-targeting properties, an optimal micellar carrier should precisely control drug release inside the cancer cell. However, therapeutic efficacy is always restricted by the gradual drug permeation for its hydrophobicity [26]. The development of stimuli-responsive carriers that quickly release encapsulated cargo triggered by intracellular environmental factor is an efficient strategy to improve drug bioavailability [27–29]. In our recent paper, we developed micelle platform with a PCB shell and disulfide linked to a biodegradable poly-ε-caprolactone (PCL) core. The carriers showed many advantages, such as ultralow protein absorption in serum and a fast intracellular drug release triggered by higher GSH intracellular concentration [30]. Herein, to enhance drug bioavailability in vivo, this micellar carrier was further optimized by introduction of a galactosamine ligand for integrating the multifunction, excellent stealth property, active targeting to hepatic carcinoma, and reductively responsive intracellular release, as showing in Scheme 1.

2. Materials and Methods

2.1. Materials

PCL-diol (, ) was purchased from Sigma-Aldrich (Shanghai, China). Cystamine dihydrochloride (Cys.2HCl) (>96%) and 1, 1-carbonyldiimidazole (CDI) (>97.0%) were purchased from the National Pharmaceutical Group Chemical Reagent (Beijing, China) and used as received. 2, 2-Azobis(isobutyronitrile) (AIBN) (97%) was purchased from J&K Chemical (Beijing, China) and recrystallized before being used as an initiator. The monomers, carboxybetaine methacrylate (CBMA, 99%), RAFT reagent (4-cyanopentanoic acid)-4-dithiobenzoate (CPADB, 98%), doxorubicin hydrochloride (DOX·HCl, 99%), N-(3-dimethylaminopropyl)-N-ethyl carbodiimide hydrochloride (EDC·HCl, 98%), and N-hydroxysuccinimide (NHS, 98%), were purchased from J&K Chemical (Beijing, China) and used as received. All other reagents and solvents were of analytical grade and used as received. Dulbecco’s modified Eagle’s medium (DMEM), penicillin-streptomycin, fetal bovine serum (FBS), and 3-[4, 5-dimethylthiazol-2-yl]-2, 5-diphenyltetrazolium bromide (MTT), were purchased from Thermo Fisher Scientific (Shanghai, China).

2.2. Synthesis of PCL Macro-RAFT Agent

For synthesis of the PCL macro-RAFT agent, two hydroxyl groups of PCL-diol were first activated by CDI and then conjugated with cystamine monomer to provide reductive disulfide bonds and reactive amino-end groups [29]. Next, the PCL macro-RAFT agent, CPADB-SS-PCL-SS-CPADB, was prepared by a condensation reaction between amino-end groups of PCL and the carboxylic group of CPADB through EDC/NHS chemistry. The detailed synthesis and characterization of the PCL macro-RAFT agent were described in our previous paper [28].

2.3. Synthesis of PC-SS-PCL-SS-PCB

PCB-SS-PCL-SS-PCB was prepared by RAFT polymerization of CBMA by using CPADB-SS-PCL-SS-CPADB as the chain transfer agent. Typically, The CPADB-SS-PCL-SS-CPADB (0.4 g, 0.140 mmol) and AIBN (4.6 mg, 0.028 mmol) were dissolved in a sealed ampoule with 4 ml dry tetrahydrofuran (THF). Then, CBMA (0.6 g, 2.618 mmol) was dissolved in 4 ml saturated salt water and placed into an above reaction tube. After three freeze-evacuate-thaw cycles, the polymerization was conducted at 70°C for 48 h. The product was purified by dialysis (bag MWCO 3000) against deionized water to remove salt and unreacted CBMA. Finally, PCB-SS-PCL-SS-PCB was obtained by lyophilization as a light pink powder (0.574 g, 57.4%).

2.4. Modification of PCB-SS-PCL-SS-PCB with Galactosamine

Targeting molecule, GAL is used to conjugate on PCB-SS-PCL-SS-PCB by an amidation reaction between the amine of GAL and carboxylate group of PCB. To accomplish the purpose, 50 mg of PCB-SS-PCL-SS-PCB was first resolved in the 4 ml mixed solution of equivoluminal dimethyl sulfoxide (DMSO) and pure water. Subsequently, the solution was incubated with 0.5 ml EDC·HCl (400 mM) and NHS (200 mM) in water for 30 min and then adjusted the pH value to 9 by adding in 10 mM sodium borate buffer. After that, 5 mg of GAL was added and reacted at room temperature (RT) for 4 h. The solution was transferred into a dialysis bag (MWCO 3500) against pure water for 48 h and then lyophilized to obtain GAL-modified PCB-SS-PCL-SS-PCB (GAL-m-polymer).

2.5. Preparation of GAL-M-Polymer Micelles

To prepare the GAL-m-polymer micelles (denoted as GAL-micelles), we used a similar procedure with that of PCB-SS-PCL-SS-PCB micelles (denoted as PCB micelles) reported in our previous paper [28]. The size and size distribution (PDI) of GAL-micelles were measured with a laser particle size analyzer (Nano ZS90, Malvern, UK). The morphology of GAL-micelles was characterized with a JEM2100 (JEOL, Japan) transmission electron microscopy (TEM) system at an operated voltage of 75 kV. For TEM observation, a drop of micelle solution was added onto the copper grid, and then, the resulting sample was air-dried and measured at RT.

2.6. DOX Loading and Release from GAL-Micelles

We used a coprecipitation method to prepare DOX-loaded GAL-micelles. Briefly, 2 mg DOX·HCl was first dissolved in DMSO and then treated by triethylamine solution (1 mg/ml) for 2 h. Subsequently, 10 mg GAL-m-polymer was added to the solution and stirred overnight. PB (50 mM, pH 7.4) was added at a rate of one drop every 6-7 s until the micellization of GAL-m-polymer. The solution was sealed using a dialysis bag (MWCO 3500) against PB at RT for 48 h, then filtered through a 0.45 μm filter for removal of the free DOX. To calculate drug loading content, lyophilized DOX-loaded GAL-micelles were dissolved in DMSO and analyzed at 485 nm with a UV-Vis spectrophotometer (UV2550, Shimadzu, Japan). Drug loading content (DLC) and drug loading efficiency (DLE) were determined by the following equations:

In vitro release profiles DOX from GAL-micelles were studied using a dialysis tube (MWCO 14000) at 37°C against PB (pH 5.0, 50 mM) and PB (pH 7.4, 50 mM) in the presence and absence of 10 mM DTT. At regular intervals, 3 ml of release media was collected and an equal volume of fresh media was added. The amount of released DOX was determined by UV-Vis spectroscopy. The release experiments were conducted in triplicate. The results showed the average value with standard deviations.

2.7. Cell Uptake Studies

The cellular uptake of DOX, DOX-loaded PCB micelles, and DOX-loaded GAL-micelles was observed by fluorescence microscopy. HepG2 and EC109 cells were seeded into 24-well plates with in 1 ml DMEM (10% FBS) and incubated at 37°C in 5% CO₂. After reaching about 80% confluence, the cells were incubated with free DOX, DOX-loaded PCB micelles, or DOX-loaded GAL-micelles, where the concentration of DOX was fixed at 5 μg/ml in each culture medium. After 4 h incubation, the cells were washed three times with PBS and then imaged by fluorescence microscopy (IX73, Olympus, Japan). After that, the cells were treated with 0.25% trypsin and resuspended in 500 μl PBS (pH 7.4) for flow cytometer (FC500, Beckman Coulter, US) measurement.

2.8. Cell Viability Assays

The cytotoxic effects of empty micelles or micelle-loading drug were determined using MTT assays. HepG2 and EC109 were seeded into 96-well plates at 5000 cells/well and cultured 24 h. The culture medium was replaced with PBS (pH 7.4) containing free DOX, DOX-loaded PCB micelles, or DOX-loaded GAL-micelles, and then, the cells were incubated for another 24 h. The medium was replaced with 200 μl of fresh medium, and 20 μl MTT (5 mg/ml in PBS) was then added to each well. After 4 h, unreacted dye was carefully removed and formazan crystals were dissolved in 200 μl/well DMSO. The plate was incubated in 37°C for 10 min before measuring absorbance at 570 nm with an ELISA microplate reader (Bio-Rad). Cell viability (%) was calculated as follows: where OD_sample is the absorbance of the cells treated by polymers and OD_control is the absorbance of the untreated cells. Each experiment was done in triplicate.

2.9. In Vivo Antitumor Studies

The nude mice bearing HepG2 tumor model were injected via the tail vein with 200 μl PBS, DOX, DOX-loaded PCB micelles, or DOX-loaded GAL-micelles at an equivalent DOX dose of 4 mg/kg every two days. The tumor size and the body weight of mice were measured before each injection. Tumor size was measured using vernier calipers and calculated using the following formula: (where is width and is length, respectively). The therapeutic efficacy of the treatment was evaluated by comparing the experimental groups with the control group.

3. Results and Discussion

3.1. Polymer Characterization

Scheme 2 represents the synthesis route of GAL-m-polymer. PCL-diol was first introduced the cystamine at the end groups [31]. Next, a PCL macro-RAFT agent was readily obtained by a conjugating reaction of amino-end groups of PCL and the carboxylic group of CPADB. PCB-SS-PCL-SS-PCB was prepared by RAFT polymerization of CBMA by using CPADB-SS-PCL-SS-CPADB as the chain transfer agent. Finally, GAL-m-polymer was prepared by modified PCB-SS-PCL-SS-PCB with GAL via EDC/NHS chemistry.

The resulting PCB-SS-PCL-SS-PCB and GAL-modified PCB-SS-PCL-SS-PCB (GAL-m-polymer) were characterized with ¹HNMR and FT-IR spectrum. ¹HNMR spectrum of GAL-m-polymer (Figure 1(a)) presents new small characteristic peaks at 1, 2, 3, 4, and 5 (δ5.2, 3.9, 3.8, 3.6, and 3.4 ppm, respectively) which are attributed to the protons of GAL [30], in addition to the characteristic protons of PCB-SS-PCL-SS-PCB [28]. FT-IR spectra were also used to determine the successful modification of PCB with GAL (Figure 1(b)). Compared with FT-IR spectrum of PCB-SS-PCL-SS-PCB, the absorption peak around 3400 cm-1 broadening in that of GAL-m-polymer indicates the increased hydroxyl after the modification. Besides, the newly emerging peaks around 1656 cm⁻¹ belongs to vibration of C=O in the amide.

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3.2. Characterization of GAL-m-Polymer Micelles

GAL-m-polymer was self-assembled into polymeric micelles in aqueous solution with PCL as a core and modified PCB as a shell. The hydrodynamic diameter distribution () of micelle was measured by DLS (Figure 2(a)). The average diameter is approximately , showing a slight change compared to that of without modification [30]. The polydispersity index (PDI) is approximately 0.18. TEM imaging revealed that the micelles of GAL-m-polymer have a spherical morphology with a mean diameter of approximately (Figure 2(b)). The difference between DLS and TEM measurements of micellar size is likely due to the shape of micelle at different hydration states, from swelled at hydrated (DLS) to collapsed at dry (TEM).

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The antifouling and redox-responsive properties of PCB micelles and GAL micelles were investigated by DLS analysis. After incubation with 50% FBS solution, both micelles show no significant changes in size even after incubation for 72 h (Figure 3(a)), indicating that the zwitterionic PCB shell effectively prevents protein adsorption from polymer micelles. High serum stability is helpful to prolong circulation in the bloodstream. Reductive response to GSH was further investigated by analyzing size change with DLS. Both micelles show an increased and broadened PDI after addition of 10 mM GSH for 12 h. As disulfides are cleavable in the presence of GSH, the PCB shells are detached from the micellar surface, resulting in micelle aggregation.

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3.3. Preparation of DOX-Loaded GAL-Micelles

The multifunctional micellar carrier prepared by GAL-M-polymer is illustrated in Figure 4(a), where the PCB segment provided antifouling capability; the conjugated GAL ligand was expected an active targeting function; PCL was used for drug encapsulation and cystamine linkers offered a reductive response. Drug loading content was determined by UV-Vis spectrophotometry in DMSO. DLC and DLE were approximately 19.6% and 47.3%, respectively. The average diameter of DOX-loaded GAL-micelles increased to and also maintained a narrow size distribution (Figure 4(b)), when compared to GAL-micelles (Figure 2(b)). TEM image showed that DOX-loaded GAL-micelles have a spherical morphology with good dispersion and a diameter of approximately (Figure 4(c)). The results illustrate surface modification with GAL ligand show little influence on drug loading and carrier’s properties [30] but may endow a novel function of active targeting to HepG2 cells. The stable structure and uniform small size facilitate intracellular uptake and EPR effect of carriers efficiently in vivo [32].

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3.4. In Vitro Drug Release

In vitro drug release profile from DOX-loaded GAL-micelles was investigated at 37°C in PBS at pH 7.4 and 5.0 with or without 10 mM GSH and as shown in Figure 5, only approximately 24% of DOX was released from GAL-micelles within 48 h at pH 7.4 without treated by GSH. As the increase of acidity to pH 5.0, the DOX release reached to 48.2% within 24 h, which is likely to result from the protonation of DOX. In comparison, an accelerated release of DOX was activated in the presence of 10 mM GSH, in which over 60% and 80% of DOX was released from GAL-micelles at both pH 7.4 and 5.0, respectively. The reductive response triggered a rapid drug release which is due to the cleavage of disulfide bonds at the surface of the core [33], leading to shell shedding and micelle aggregating, followed by fast drug efflux during the reassembly of deprotected micelles [34].

3.5. In Vitro Cytotoxicity and Cell Uptake

In vitro cytocompatibility of PCB micelles and GAL-micelles was evaluated with MTT assays in HepG2 and EC109 cells. Cells without treatment were used as control and showed a viability of 100%. As shown in Figure 6(a), the viability of HepG2 and EC109 cell was over 90% incubation of both micelles, even at a concentration up to 200 mg/l. The micelles possess low cytotoxicity which was likely due to the biocompatible PCB, PCL, and GAL ligand. For the cytotoxicity assays, HepG2 and EC109 cells were incubated with free DOX, DOX-loaded PCB micelles, and DOX-loaded GAL-micelles (Figure 6(b)). The inhibitory concentrations to produce 50% of cell death (IC50) in HepG2 cells were 0.26 mg/l, 1.44 mg/l, and 0.72 mg/l for free DOX, DOX-loaded PCB micelles, and DOX-loaded GAL-micelles, respectively (Figure 6(b)). The DOX-loaded PCB micelles showed significantly lower cytotoxicity than free DOX, which may be due to less efficient cell uptake caused by the stealth shielding shell of zwitterionic PCB [15, 16]. After the functionalization with GAL, DOX-loaded GAL-micelles exhibited increased inhibition of cellular proliferation when compared with DOX-loaded PCB micelles. However, DOX-loaded PCB micelles and DOX-loaded GAL-micelles showed similar antitumor activity in EC109 cells.

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Figure 6

Toxicity of PCB micelles and GAL-micelles (a, b) and free DOX, DOX-loaded PCB-micelles, and DOX-loaded GAL micelles in HepG2 and EC109 cells incubated for 24 h. Data are presented as the average (standard deviation ()); fluorescence microscopy images of HepG2 (c) and EC109 cells (d) incubated with empty GAL-micelles (A), DOX-loaded PCB-micelles (B), and DOX-loaded GAL-micelles (C) for 4 h, where the concentration of DOX was fixed at 5 μg/ml. The scale bars correspond to 50 μm in all the images.

DOX is a popular chemotherapeutic drug and widely used in clinics for treating various hematological malignancies and solid tumors. Mechanistically, the insertion of DNA into tumor cells inhibits macromolecular biosynthesis, eventually leading to cell apoptosis [35, 36]. Intracellular drug accumulation depends on the efficacy of cell uptake and drug release from the loading carrier [37]. The increased therapeutic effect of DOX-loaded GAL-micelles in HepG2 cells can be attributed to improve cell uptake via active targeting, as demonstrated by fluorescence microscopy (Figure 6(c)). Indeed, empty micelles had no fluorescence signal, whereas the red fluorescence of DOX was easily detectable (Figure 6(c), B), showing that DOX is efficiently released from DOX-loaded PCB micelles in response to intracellular GSH. Furthermore, DOX fluorescence in the cytoplasm and nucleus was brighter and more intense in DOX-loaded GAL-micelles (Figure 6(c), C), consistent with the increased cell uptake due to GAL binding to ASGP receptors on the surface of HepG2 cells [22]. However, DOX-loaded GAL-micelles showed a similar DOX fluorescence signal than DOX-loaded PCB micelles in EC109 cells, suggesting that active targeting of GAL is less effective in this cell type (Figure 6(d)). These results are consistent with the toxicity studies described above. Together, our data demonstrate that DOX-loaded GAL-micelles possess outside active targeting and inside redox-responsive release in HepG2 cells, suggesting they are promising nanocarriers for efficient treatment of liver cancer in vivo.

3.6. In Vivo Antitumor Efficacy

The antitumor efficacy of DOX-loaded micelles was investigated in vivo by using a nude mice bearing tumor model of human liver cancer. When the tumor size reached approximately 100 mm³, PBS, free DOX, DOX-loaded PCB micelles, or DOX-loaded micelles GAL were injected into the tumor-bearing mice through the tail vein. Tumor volume and body weight were measured and plotted as a function of time (Figure 7). As shown in Figure 7(a), the tumor volume in mice treated with PBS increased rapidly. In contrast, in the other groups, the tumors showed a slow growth, particularly, tumors in mice injected with DOX-loaded GAL-micelles. The body weight of mice treated with free DOX showed a clear decrease in weight as a result of in vivo cytotoxicity [21] (Figure 7(b)), the mice in the other groups exhibited a slow increase in body weight. More importantly, mice treated with DOX-loaded GAL-micelles had the smallest increase in weight within 12 days, suggesting the most effective tumor inhibition. Excellent stealth property from zwitterionic shells provides drug-loaded micelles a prolonged circulation time [38, 39] and enhanced drug accumulation at tumor site via EPR effect. The active targeting of DOX-loaded GAL-micelles to HepG2 cells further improves cell uptake. Finally, DOX is rapidly released due to reductive cleavage of disulfide bonds inside HepG2 cells.

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4. Conclusions

The multifunctionality of polymeric micelle carrier, including high antifouling ability, redox responsive property, and active targeting in hepatic carcinoma cells, was successfully achieved by the modification of a triblock copolymer with disulfide-linked zwitterionic and biodegradable polymer (PCB-SS-PCL-SS-PCB) with galactosamine. GAL-micelles loaded with DOX exhibit rapid drug release under reductive environment, enhanced drug levels, and antitumor activity in HepG2 cells. As expected, this carrier revealed better anticancer efficacy in hepatic tumor-bearing mice than free DOX or no-targetable micelles. Thus, multifunctional nanocarriers with a flexible design of zwitterionic polymeric micelles represent a valuable strategy for improving drug bioavailability in the treatment of liver cancer.

Data Availability

The authors confirm that the data supporting the findings of this study are available within the article.

Conflicts of Interest

The authors declare no conflict of interest.

Acknowledgments

The authors gratefully acknowledge the financial support from the National Natural Science Foundation of China (Project U1704150) and Scientific and Technological Projects of Henan province (182102410017).

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Copyright © 2020 Jingming Zhai et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

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