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A facile adenosine triphosphate‑responsive nanoplatform for efficacious therapy of esophageal cancer

  • Authors:
    • Jinglong Wang
    • Linhao Xu
    • Xiaotong Liu
    • Ronghua Yang
    • Dong Wang
  • View Affiliations

  • Published online on: August 10, 2020
  • Article Number: 108
  • Copyright: © Wang et al. This is an open access article distributed under the terms of Creative Commons Attribution License.

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Current chemotherapeutic agents against esophageal cancer (EC) are suboptimal. To improve treatment efficacy, a nanoplatform based on ATP‑responsive drug release was developed for EC therapy. First, the chemotherapeutic agent epirubicin (EPI) was inserted into an ATP aptamer (Ap) to form double‑stranded DNA (‘DNA duplex’). Subsequently, polyethyleneimine (PEI) was employed to condense the EPI‑loaded duplex to construct the final nanoplatform (PEI‑Ap‑EPI). Following internalization by cancer cells, the EPI‑loaded DNA duplex could open and release EPI in an intracellular ATP‑rich environment. An in vitro drug‑release assay demonstrated that ~50% of EPI was released from PEI‑Ap‑EPI in an ATP‑rich condition. However, only 15% of EPI was released in the presence of a low concentration of ATP. In vitro cytotoxicity and apoptosis assays demonstrated that PEI‑Ap‑EPI could enhance EPI efficiency against EC cells markedly compared with those in the control group. Therefore, this facile PEI‑Ap‑EPI nanoplatform may be a promising strategy to improve the efficacy of EPI treatment in EC.


Esophageal cancer (EC) was the sixth leading cause of cancer-associated mortality worldwide in 2014 (1). Adenocarcinoma and squamous cell carcinoma are the primary types of EC (2). Squamous cell carcinoma is more common in Asia and developing countries (3), and its prognosis is poor (4).

Chemotherapy is a routine method for EC treatment. Commonly used chemotherapeutic agents include platinum drugs, taxanes and epirubicin (EPI) (5). However, low solubility in water and poor selective capability have greatly limited the clinical application of chemotherapeutic agents (6). Therefore, it is necessary to develop a novel drug delivery system (DDS) to enhance drug solubility, promote drug accumulation in tumor cells and achieve ‘on-demand’ drug release, to result in increased efficacy of EC treatment.

Recently, DDSs based on nanoparticles have been developed to deliver antitumor drugs. For example, Fan et al (5) developed EPI-loaded near infrared fluorescent peptide nanoparticles for esophageal cancer therapy; the results revealed that these nanoparticles could significantly enhance the efficiency of EPI and decrease its system toxicity. These ‘nano-DDSs’ can improve the water solubility, biocompatibility, and tumor-tissue accumulation of a drug via the enhanced permeability and retention effect, and reduce the side effects of a drug (79). To achieve on-demand release of a drug, various stimuli-responsive DDSs have been developed. Various endogenous signals, such as pH and glutathione, have been employed as stimuli to trigger drug release (10). For example, Zhang et al (11) developed a redox-responsive polymeric micelle co-loaded paclitaxel/apatinib for effectively reversing cancer multidrug resistance; the results revealed that in the presence of glutathione, both drugs could rapidly be released to kill cancer cells.

ATP is considered the ‘molecular unit of currency’ of intracellular energy transfer. ATP exhibits a high concentration in the cytosol of tumor cells (1–10 mM) compared with the extracellular concentration of ATP (<0.4 mM) (12). Therefore, ATP can serve as a stimulus to trigger the release of chemotherapeutic agents.

Aptamers are oligonucleotide/peptide molecules that bind to a specific target molecule (13). Binding of aptamers to ATP has been reported to promote release of preloaded therapeutics directly through a ‘conformational switch’ that is recognized and activated specifically by ATP (1416).

Anthracyclines are traditional anticancer drugs. They can destroy cancer cells efficaciously because they interact with the GC pairs of DNA, and inhibit the growth of tumor cells by interfering with DNA transcription (17). Therefore, anthracyclines can be loaded into double-stranded DNA (‘DNA duplex’)-containing GC pairs.

In the present study, a nano-DDS composed of an ATP aptamer (Ap) and its complementary single-stranded DNA (cDNA), EPI and polyethyleneimine (PEI) was developed. First, the Ap interacted with cDNA to form a duplex by complementation. Subsequently, EPI was loaded into the duplex DNA through interaction with the GC pairs in the duplex (Ap-EPI). Finally, PEI (which has a positive charge) underwent electronic interaction with the DNA duplex to condense the DNA duplex into nanoparticles (Fig. 1). It was hypothesized that PEI-Ap-EPI nanoparticles could increase accumulation in tumor cells and release EPI rapidly in the presence of a high level of ATP, thereby improving treatment efficacy considerably.

Materials and methods


The Ap (5′-ACCTGGGGGAGTATTGCGGAGGAAGGT-3′), cDNA of the Ap (5′-ACCTTCCTCCGCAATACTCCCCCAGGT-3′), control aptamer (5′-ACCTGGTTTAGGCGGCTCGGGAAT-3′) and cDNA of the control aptamer (5′-ATTCCCGAGCCGCCTAAACCAGGT-3′) were purchased from Sangon Biotech Co., Ltd. Trypan Blue dye was obtained from Generay Biotech Co., Ltd. RPMI-1640 medium and FBS were purchased from Invitrogen; Thermo Fisher Scientific, Inc. Penicillin was supplied by CSPC Pharmaceutical Group, Ltd. Streptomycin was obtained from Merro Pharmaceutical Co., Ltd. MTT was purchased from Sigma-Aldrich; Merck KGaA. PBS was obtained from Beyotime Institute of Biotechnology. Ethylenediaminetetraacetic acid and MgCl2 were obtained from Sinopharm Chemical Reagent Co., Ltd. Water was purified and deionized using a Milli-Q™ system from EMD Millipore.

Cell culture

The EC KYSE-70 and EC109 cell lines were obtained from the American Type Culture Collection, and incubated in RPMI-1640 medium supplemented with 10% (v/v) FBS, 100 U/ml penicillin and 100 mg/ml streptomycin in an atmosphere of 5% CO2 at 37°C. Cells were counted using a hemocytometer (Sigma-Aldrich; Merck KGaA). Cell viability was assessed by exclusion of Trypan Blue dye (0.4%). In brief, 10 µl Trypan Blue dye solution was added to 100 µl cell suspension, and maintained at room temperature for 3–5 min. Subsequently, 10 µl cells suspension was added onto the hemocytometer and observed using a Nikon TS100 light microscope (Nikon Corporation).

DDS preparation

The Ap and its cDNA were dissolved in PBS supplemented with MgCl2 (5 mM), mixed and agitated for 24 h at room temperature. Subsequently, EPI was added to the DNA duplex and incubated for 2 h at room temperature to form Ap-EPI. The amount of intercalated EPI was determined based on the fluorescence intensity, which was recorded using a microplate reader (Tecan Group, Ltd.).

Next, PEI-Ap-EPI nanoparticles were created. Briefly, Ap-EPI (2.5 µM) was reacted with branched PEI (25 k) at a ratio of 1:2 in aqueous solution for 1 h at room temperature. Excess PEI was removed by centrifugation at 2,000 × g for 5 min at room temperature. As a result, PEI-Ap-EPI was obtained. The final nanoparticles were prepared by resuspending PEI-Ap-EPI in ultrapure water.

The morphology of PEI-Ap-EPI nanoparticles was determined by transmission electron microscopy (TEM) using a Tecnai G2 system (FEI; Thermo Fisher Scientific, Inc.) and their size distribution was determined by differential light scattering (DLS) using a Zs90 setup (Malvern Instruments, Ltd.).

Characterization of Ap-EPI

Ap-EPI (1.5 µM) was incubated with ATP (0, 0.2, 0.4, 1, 2, 4 and 8 mM) for 15 min at 37°C, and the fluorescence intensity was measured to evaluate the ATP response of Ap-EPI. To evaluate the specificity of the ATP response, Ap-EPI (2 µM) was added to PBS supplemented with MgCl2 (5 mM), and incubated with ATP, GTP, uridine triphosphate (UTP) or cytidine triphosphate (CTP), respectively, for 15 min at 37°C. All compounds were used at 0, 0.5, 1, 2, 4 and 8 mM, respectively. Finally, fluorescence spectroscopy of EPI was performed at an excitation wavelength of 480 nm to examine the specificity of Ap-EPI.

ATP-triggered EPI release in vitro

A total of 2 mg of PEI-Ap-EPI (containing 224 µg EPI) was dispersed into PBS containing 5 mM MgCl2. Subsequently, ATP (0.4 and 4 mM) was added, and the mixture was incubated at 37°C for 0, 0.5, 1, 2, 4, 8, 12 or 24 h. The amount of EPI released was determined via measurement of fluorescence intensity at the aforementioned time points. In addition, PEI-control (Ctrl) Ap-EPI mixed with ATP (4 mM) was used as a negative control.

Stability of PEI-Ap-EPI nanoparticles

To determine the stability of PEI-Ap-EPI nanoparticles, they were dispersed in PBS with 10% FBS and incubated at 37°C. The size distribution and zeta potential of PEI-Ap-EPI nanoparticles were measured using DLS at 0, 2, 4, 6, 8, 12 and 24 h.

EPI accumulation in cells

EPI accumulation in KYSE-70 and EC109 cells was measured by fluorescence microscopy. Cells (~105 cells/well) were seeded in a six-well plate. After 24 h, EPI (0.5 µg/ml), Ap-EPI and PEI-Ap-EPI dispersed in serum-free medium were added to the six-well plate, and incubated at 37°C for another 24 h. Subsequently, the drugs were removed and cells were washed three times with PBS. Subsequently, cells were incubated with 4% paraformaldehyde for 15 min at room temperature. Finally, confocal laser scanning microscopy (CLSM) was performed using an LSM 710 setup (Zeiss AG) after cells had been treated with an anti-fluorescence quencher.

Cell viability assay

KYSE-70 and EC109 cells were seeded into 96-well plates at a density of 5×103 cells per well and cultured in medium for 24 h. Then, these two cell lines were treated with increasing concentrations (0.1, 0.5, 1, 2, 4, 8 and 16 µg/ml EPI for KYSE 70 cells; 0, 0.06, 0.16, 0.32, 0.64, 1.28 and 2.56 µg/ml EPI for EC109 cells; different concentrations were used due to the different sensitivity of the cells to EPI) of free EPI, Ap-EPI or PEI-Ap-EPI, and incubated at 37°C for 48 h. Afterwards, these drugs were removed and 20 µl MTT (5 mg/ml) was added to each well and incubated for another 4 h. Finally, the medium in each well was replaced with 150 µl dimethyl sulfoxide. The absorbance was scanned at 490 nm by FlexStation™ 3 (Molecular Devices, LLC). Each experiment was repeated at least three times. The IC50 value was calculated using GraphPad Prism 6 (GraphPad Software, Inc.).

Apoptosis detection

Apoptosis of KYSE-70 and EC109 cells was detected using the APO-BrdU TUNEL Assay kit (Life Technologies; Thermo Fisher Scientific, Inc.), according to the manufacturer's protocol. These two cell types were seeded in six-well plates at a density of 105 cells per well. Following culture for 12 h, KYSE-70 cells were incubated with 0.5 µg/ml EPI, Ap-EPI or PEI-Ap-EPI for another 12 h. EC109 cells were treated with the three formulations of EPI (0.1 µg/ml) for 12 h. Subsequent steps were carried out in accordance with the manufacturer's protocol. In brief, cells were stained with BrdU solution (10 µM) at 37°C for 2 h, washed with PBS for three times, fixed using 4% formaldehyde at room temperature for 15 min, washed with PBS for three times, incubated with Triton X-100 permeabilization buffer (1 ml/well) for 20 min at room temperature, cultured with 2N HCl (1 ml) for 10 min at room temperature, incubated with phosphate/citric acid buffer (pH 7.4, 1 ml/well) for 10 min at room temperature, washed with Triton X-100 permeabilization buffer, stained with anti-BrdU primary antibody at room temperature overnight, washed with Triton X-100 permeabilization buffer, and finally stained with FITC-labeled secondary antibody at room temperature for 1 h. Cells were observed under a fluorescence microscope (magnification, ×40; Leica Microsystems GmbH). Green fluorescence indicated apoptotic cells. Nuclei were stained with DAPI (10 µg/ml) at room temperature for 15 min and emitted blue fluorescence. Apoptosis of KYSE70 and EC109 cells following treatment with the three drugs was assessed by counting the percentage of apoptotic cells (green) among the total cells (blue) according to the method of Takeda et al (18).

Determination of cell cycle phases

For analyses of cell cycle arrest, KYSE70 and EC109 cells were seeded in a six-well plate at a density of 105 cells per well and incubated with EPI, Ap-EPI or PEI-Ap-EPI for 48 h. Then, cells were collected and fixed with 70% ethanol overnight at 4°C. Cells were washed with PBS, exposed to PI/RNase staining buffer (BD Biosciences) and incubated in the dark for 30 min. Cells were counted using a flow cytometer (FACScalibur™; BD Biosciences) and analyzed using FlowJo 7.6 (FlowJo LLC) (19).

Statistical analysis

Each experiment was repeated three times. Numerical data are presented as the mean ± SD. One-way single factorial ANOVA followed by Tukey's post hoc test was performed to determine statistical significance of the data using SPSS software (version 19.0; IBM Corp.). P<0.05 was considered to indicate a statistically significant difference.


EPI loading and ATP-response release

First, an Ap and its cDNA were hybridized to construct a carrier to load free EPI. The Ap has 27 base pairs rich in GC that can accommodate EPI (12). To evaluate the number of EPI molecules loaded into the ATP-Duplex, changes in the fluorescence intensity of EPI were measured when it was mixed with various concentrations of the ATP-Duplex. Different concentrations of the ATP-Duplex were added to a fixed concentration of EPI. It was demonstrated that the fluorescence intensity of EPI decreased with an increasing concentration of the ATP-Duplex. Fluorescence nearly disappeared when the molar ratio of duplex: EPI was 1:2 (Fig. 2A).

In the present design, the duplex dissociated once the Ap combined with ATP [which has a different extracellular concentration (<0.4 mM) and cytosol concentration (1–10 mM)], and then EPI was released from the ATP-Duplex. Therefore, to assess the ATP-Duplex response to ATP, the fluorescence intensity of released EPI was recorded after Ap-EPI (1.5 µM) had been incubated with ATP (0, 0.2, 0.4, 1, 2, 4 or 8 mM). In the ATP-Duplex group, the fluorescence intensity strengthened upon a gradual increase in the ATP concentration. When the ATP concentration reached 4 mM, the fluorescence intensity of EPI was 2-fold higher than that when the ATP concentration was 0.4 mM (Fig. 2B). These results suggested that the ATP-Duplex was sensitive to ATP, and that EPI release was dependent on the ATP concentration.

To demonstrate the specificity of ATP-triggered EPI release, the release of EPI from Ap-EPI was investigated under GTP, UTP and CTP conditions. Ap-EPI (2 µM) was treated with GTP, UTP, CTP or ATP at different concentrations for 12 h, and EPI release was measured using a microplate reader. EPI release was low from Ap-EPI following incubation with GTP, UTP or CTP (Fig. 2C). Furthermore, when the concentration of GTP, UTP and CTP increased to 8 mM, ~5% of fluorescence was recovered. Conversely, fluorescence recovery was ~40% when 8 mM ATP was added, which was 8-fold higher than that when GTP, UTP or CTP was added. This result illustrated that the ATP-Duplex response to ATP was specific.

Preparation and characterization of PEI-Ap-EPI

Dizaj et al (20) demonstrated that the DNA formed in nanoparticles can protect them from enzymatic digestion. To avoid the EPI-loaded DNA duplex being digested by enzymes during administration, PEI (a polymer molecule with a positive charge) was employed to condense Ap-EPI into nanoparticles through charge interaction. To confirm this phenomenon, the zeta-potential changes on the surface of Ap-EPI were measured. The surface charge of Ap-EPI was −20.4 mV, whereas its zeta potential changed to positive (~15.5 mV) after it interacted with PEI (Fig. 3A). This result demonstrated that Ap-EPI interacted completely with PEI. In addition, the size distribution and morphology of PEI-Ap-EPI were examined further by DLS and TEM, respectively. The size of PEI-Ap-EPI measured by DLS was ~100 nm and the polydispersity index was 0.2 (Fig. 3B), demonstrating that PEI-Ap-EPI was small and of narrow dispersion. In accordance with the results of DLS, TEM also revealed a uniform spheroid structure of size ~100 nm (Fig. 3C). Additionally, PEI-Ctrl-EPI exhibited a narrow dispersion with uniform spheroid structure (Fig. 3D and E).

Subsequently, to evaluate the ATP-responsivity of PEI-Ap-EPI, the EPI released from PEI-Ap-EPI nanoparticles triggered by ATP was investigated. Typically, ATP of various concentrations was added to PEI-Ap-EPI solutions and incubated for 24 h at 37°C. The fluorescence of PEI-Ap-EPI solutions at different time points was recorded to depict the profile of EPI release (Fig. 4A). After 24 h, >50% EPI was released from PEI-Ap-EPI in the presence of 4 mM ATP, which was significantly higher compared with the control groups, exhibiting a time-dependent release. In the 0.4 mM ATP group, ~15% EPI was released. Notably, in the PEI-Ctrl-EPI group, only ~18% EPI was released after 24 h in the presence of 4 mM ATP, indicating that PEI-Ctrl-EPI exhibited little response to ATP.

To investigate the stability of PEI-Ap-EPI, the particle size and zeta potential were monitored for 24 h when it was incubated in PBS with 10% FBS at pH 7.4. There was little change in particle size and zeta potential, which demonstrated that PEI-Ap-EPI was quite stable in the circulation (Fig. 4B).

Intracellular accumulation

Sufficient accumulation of a drug in cancer cells is indispensable for efficacious treatment (21). In the present study, intracellular accumulation of EPI, Ap-EPI and PEI-Ap-EPI was measured via fluorescence imaging using CLSM after KYSE-70 and EC109 cells had been treated with these three formulations (Fig. 5). The fluorescence intensity was strongest following treatment with PEI-Ap-EPI, showing the greatest intracellular accumulation. This result could have been due to PEI-Ap-EPI having greater drug loading and being internalized more readily by cancer cells due to the reversal of surface charge after Ap-EPI coating with PEI. Ap-EPI showed low accumulation. The negative surface charge of Ap-EPI likely impeded its internalization.

Cytotoxicity in vitro

The toxicity of EPI, Ap-EPI and PEI-Ap-EPI in KYSE-70 and EC109 cells was evaluated using an MTT assay. The cytotoxicity of the drugs increased with increasing drug dose (Fig. 6). In KYSE-70 cells, the IC50 of PEI-Ap-EPI was 2 µg/ml, which was lower than that of EPI (2.5 µg/ml), but the IC50 of Ap-EPI (7.5 µg/ml) was ~3- and 3.7-fold higher than that of EPI and PEI-Ap-EPI, respectively. In EC109 cells, the IC50 of PEI-Ap-EPI was 0.41 µg/ml, which was markedly lower than that of EPI and Ap-EPI, and this was consistent with the result in KYSE-70 cells. The reason may be that, without a PEI coating, the surface negative charge of Ap-EPI limits its internalization, impeding its response to extracellular ATP (which is at a low concentration). This result demonstrated that PEI-Ap-EPI had the highest toxicity in KYSE-70 and EC109 cells.

TUNEL assay

The TUNEL assay was utilized to demonstrate the DNA damage that PEI-Ap-EPI can elicit. After KYSE-70 and EC109 cells were incubated with EPI, Ap-EPI or PEI-Ap-EPI, a TUNEL assay was performed and fluorescence microscopy was used to capture images. Blue fluorescence indicated nuclei whereas green fluorescence indicated apoptotic cells (Fig. 7A). In the PEI-Ap-EPI group, more green fluorescence was observed, indicating that it caused more severe damage than the other two groups. After counting the number of apoptotic cells in the three groups, it was demonstrated that PEI-Ap-EPI had the strongest ability to cause DNA damage. The apoptotic index (AI) in KYSE-70 cells was ~25%, which was higher than that of EPI (18%; P=0.008) and Ap-EPI (10%; P=0.005), respectively (Fig. 7B). The AI of PEI-Ap-PEI in EC109 cells was similar to that in KYSE cells (~23%) and the AI of EPI and Ap-EPI was 17% (P=0.007) and 10% (P=0.004), respectively (Fig. 7C).

Cell cycle arrest

To investigate the influence of different formulations of EPI on cell-cycle arrest, cells at each phase were counted by flow cytometry (Fig. 8). In KYSE70 and EC109 cells, after they had been treated with the three formulations of EPI, the proportion of cells in the G0/G1 phase was the greatest, and the cell cycle distribution did not differ among the three formulations.


Chemotherapy is a conventional way to inhibit tumor growth. However, some disadvantages, such as poor selectivity, weaken the efficacy of chemotherapy. Therefore, overcoming the shortcomings of chemotherapeutics to improve the efficacy of EC therapy would be helpful, and using nanoparticles for drug delivery may be an effective method.

ATP is considered to be the ‘molecular unit of currency’ of intracellular energy transfer. ATP is present at high concentrations in the cytosol of tumor cells (1–10 mM) compared with the extracellular concentration of ATP (<0.4 mM) (12). The distinct difference in the ATP levels between the extracellular and intracellular milieu is the biological principle for the design of ATP-responsive carriers. In the present study, an ATP-responsive nanoplatform for EPI delivery for EC treatment was developed. It was demonstrated that an Ap composed of 27 base pairs rich in GC accommodated EPI following interaction with its cDNA. The in vitro drug release experiments demonstrated that EPI can be rapidly released in the presence of intracellular ATP (4 mM), but only a small amount of EPI is released in the presence of extracellular ATP (0.4 mM). These actions contributed to high drug loading and release of the active drug in cells, resulting in toxicity to tumor cells.

PEI was selected to condense the DNA duplex due to four main reasons. First, through the charge interaction between PEI and DNA duplex, nanoparticles can be formed, which contribute to drug accumulation in tumor tissues (22). Second, condensation with PEI can overcome DNA instability in vivo and reduce premature leakage of EPI (12). Third, PEI can become protonated in the acid environment of lysosomes, resulting in disassembly of PEI-Ap-EPI nanoparticles and promotion of DNA-duplex escape from lysosomes (23), which, ultimately, helps to enhance therapy efficacy. Fourth, the DNA duplex can have a negative charge, thereby impeding its internalization by cancer cells (24). Following interaction with PEI, the charge of the obtained nanoparticles changed to positive, which was conducive to cell internalization.

KYSE-70 and EC109 cells were used to investigate the efficacy of PEI-Ap-EPI. It was demonstrated that more EPI accumulated in cells after they had been treated with PEI-Ap-EPI. A possible reason is that PEI-Ap-EPI has more drug-loading sites and is internalized more readily by cancer cells due to surface-charge reversal after Ap-EPI coating with PEI. The group treated with Ap-EPI exhibited little accumulation of EPI. The negative surface charge of Ap-EPI likely impeded its internalization.

In in vitro cytotoxicity experiments, the low IC50 of PEI-Ap-EPI could be explained by relatively high drug loading and effective internalization. In accordance with this hypothesis, absence of PEI coating resulted in poor internalization, which contributed to the high IC50. The TUNEL assay result was consistent with the data from experiments on intracellular accumulation and the MTT assay. These results suggested that PEI-Ap-EPI had improved efficacy for EC cells. In addition, the present study investigated the influence of drug formulations on cell cycle arrest and but did not find a significant difference among them.

The main limitation of the present study was the lack of in vivo experiments. Clinical application of the nano-DDS can occur only after rigorous in vivo experiments have been completed.

In conclusion, a novel DDS (PEI-Ap-EPI nanoparticles) for EC treatment was constructed. PEI-Ap-EPI nanoparticles of size ~100 nm were responsive specifically to a high concentration of ATP in EC cells, and were stable in the presence of FBS. In vitro experiments demonstrated that PEI-Ap-EPI could increase EPI accumulation in tumor cells. PEI-Ap-EPI showed higher cytotoxicity, and caused more severe DNA damage than Ap-EPI and EPI. These results illustrated that the novel nano-DDS may be efficacious in EC treatment, and has higher efficacy than EPI alone.


Not applicable.


The present study was supported by the Qingdao University Development and Innovation Found (grant no. 201825QUDIF124).

Availability of data and materials

The datasets used and/or analyzed during the present study are available from the corresponding author on reasonable request.

Authors' contributions

JW and LX conceived the study, and analyzed and interpreted the data. XL performed the experiments, analyzed data and wrote the manuscript. RY and DW performed the experiments and analyzed data. JW and DW designed experiments, analyzed the data, polished the manuscript and guided the reply to the comments. All authors read and approved the final manuscript.

Ethics approval and consent to participate

Not applicable.

Patient consent for publication

Not applicable.

Competing interests

The authors declare that they have no competing interests.



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Wang J, Xu L, Liu X, Yang R and Wang D: A facile adenosine triphosphate‑responsive nanoplatform for efficacious therapy of esophageal cancer. Oncol Lett 20: 108, 2020
Wang, J., Xu, L., Liu, X., Yang, R., & Wang, D. (2020). A facile adenosine triphosphate‑responsive nanoplatform for efficacious therapy of esophageal cancer. Oncology Letters, 20, 108.
Wang, J., Xu, L., Liu, X., Yang, R., Wang, D."A facile adenosine triphosphate‑responsive nanoplatform for efficacious therapy of esophageal cancer". Oncology Letters 20.4 (2020): 108.
Wang, J., Xu, L., Liu, X., Yang, R., Wang, D."A facile adenosine triphosphate‑responsive nanoplatform for efficacious therapy of esophageal cancer". Oncology Letters 20, no. 4 (2020): 108.