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A Dual pH-Responsive DOX-Encapsulated Liposome Combined with Glucose Administration Enhanced Therapeutic Efficacy of Chemotherapy for Cancer
Authors Zhai L, Luo C, Gao H, Du S, Shi J , Wang F
Received 29 January 2021
Accepted for publication 22 March 2021
Published 10 May 2021 Volume 2021:16 Pages 3185—3199
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Editor who approved publication: Dr Yan Shen
Luoping Zhai,1 Chuangwei Luo,1 Hannan Gao,1 Shuaifan Du,1 Jiyun Shi,2 Fan Wang1– 3
1Medical Isotopes Research Center and Department of Radiation Medicine, School of Basic Medical Sciences, Peking University Health Science Center, Beijing, 100191, People’s Republic of China; 2Key Laboratory of Protein and Peptide Pharmaceuticals, CAS Center for Excellence in Biomacromolecules, Institute of Biophysics, Academy of Sciences, Beijing, 100101, People’s Republic of China; 3Bioland Laboratory (Guangzhou Regenerative Medicine and Health Guangdong Laboratory), Guangzhou, 510005, People’s Republic of China
Correspondence: Fan Wang
Medical Isotopes Research Center and Department of Radiation Medicine, School of Basic Medical Sciences, Peking University Health Science Center, Beijing, 100191, People’s Republic of China
Email [email protected]
Key Laboratory of Protein and Peptide Pharmaceuticals, CAS Center for Excellence in Biomacromolecules, Institute of Biophysics, Academy of Sciences, Beijing, 100101, People’s Republic of China
Email [email protected]
Background: The acidic microenvironment of cancer can promote tumor metastasis and drug resistance. Acidic tumor microenvironment-targeted therapy is currently an important means for treating tumors, inhibiting metastasis, and overcoming drug resistance. In this study, a dual pH-responsive DOX-encapsulated liposome ([email protected]) was designed and fabricated for targeting the acidic tumor microenvironment. On the one hand, the response of acid-sensitive peptide (DVar7) to the acidic tumor microenvironment increased the uptake of liposomes in tumors and prolonged the retention time; on the other hand, the response of acid-sensitive phospholipid (DOPE) to the acidic tumor microenvironment improved the controlled release of DOX in tumors.
Methods: The acid-sensitive peptide DVar7 modified liposomes can be obtained by simple incubation of DSPE-DVar7 with DOX-loaded DOPE liposomes ([email protected]). The tumor targeting of the dual pH-responsive liposome was investigated in vitro and in vivo by near-infrared fluorescence imaging. The tumor therapeutic efficacy of [email protected] was evaluated in breast cancer mouse model using the traditional liposome as a control. Moreover, we regulated the tumor microenvironment acidity by injecting glucose to further enhance the therapeutic efficacy of cancer.
Results: DVar7 can allosterically insert into the tumor cell membrane in the acidic tumor microenvironment to enhance the tumor uptake of liposomes and prolong the retention time of liposomes in tumor. In addition, the therapeutic efficacy of pH-responsive liposomes can be further enhanced by glucose injection regulating the acidity of tumor microenvironment.
Discussion: DVar7 modified acid-sensitive nanocarriers combined with acidity regulation have great potential to improve drug resistance in clinical practice, thus improving the response rate and therapeutic effect of chemotherapy.
Keywords: dual pH-responsive, liposomes, DOX, tumor, pH (low) insertion peptide
Tumor microenvironment (TME), supporting the survival and development of cancer cells, has the special physical and chemical characteristic, such as low concentration of oxygen and low pH value, which not only play a key role in tumor progression and metastasis but also has an obvious impact on the therapeutic efficacy of tumors.1–4 In the acidic microenvironment of tumors, weakly alkaline drug molecules are easily protonated, preventing them from entering tumor cells and thus causing drug resistance. Therefore, investigating the regulatory effect of acidic TME on chemotherapy will help improving the resistance of chemotherapeutic drugs, thereby increasing the response rate and treatment efficacy of chemotherapy.5–9
In general, the extracellular pH in most tumor microenvironment is 6.5 to 6.8, and that of the endosome/lysosome is 4.5 to 6.5, both lower than the pH of normal tissues and blood (7.2 to 7.4).10 Taking advantage of this characteristic of tumors, researchers have developed various acidic pH-responsive nanocarriers, such as pH-responsive hydrogels, micelles, liposomes, and multiple sensitive materials.3,11 Among different pH-responsive nanocarriers, pH-responsive liposomes have been most investigated owing to their excellent biocompatibility and versatile modifiability.12 The pH-responsive liposomes have been widely used to replace conventional liposome to improve the delivery efficiency of chemotherapeutic drugs, toxins, and siRNA.11,13 These pH-responsive liposomes were mainly focused on the controlled release of drugs under acidic conditions.14 The most commonly used acid-sensitive strategy is using 1,2-dioleoyl-sn-glycerol-3-phosphoethanolamine (DOPE) and weakly amphiphilic acid, cholesterol hemisuccinate (CHEMS) as the composition of the liposomes.15 The results showed that under the acid condition of lysosome, pH-responsive liposomes transformed into the hexagonal crystal phase, which accelerated the release of drugs.16–19 However, many improvements are still needed to enhance the delivery efficiency of pH-responsive liposomes, such as tumor-targeting, stability, drug encapsulation efficiency. Nanoparticles that rely on the passive targeting of the EPR effect are likely to be highly enriched in the liver and cause greater toxicity, which may lead to clinical application failure.20,21 Actively targeted and stealth nanoparticles can reduce non-specific uptake in the liver and improve the efficiency of drug delivery to tumors. Stealth nanoparticles can be achieved simply by adding PEG components.22,23 Targeting capabilities can also be achieved by introducing targeting molecules into nanomaterials. Targeting molecules such as aptamers,24 antibodies, peptides,25 and ligands26 have been modified to pH-sensitive liposomes to improve its tumor targeting. However, due to the heterogeneous of human tumor,27,28 these methods have some limitations.
Previously, a family of pH (low) insertion peptide (pHLIP) have been developed. The structure of pHLIP is random under neutral or alkaline condition, but in a slightly acidic microenvironment, it forms an alpha helix to insert into the cell membrane,29–32 thereby giving pHLIP the ability to target acidic TME.29–32 The in vitro cell experiments showed that pHLIP-modified dual pH-responsive liposomes significantly improved the payload delivery and release efficiency compared with the original mono pH-responsive liposomes.33,34 Therefore, the pHLIP-mediated dual pH-responsive liposomes might have great potential to improve the in vivo tumor-targeted delivery efficiency of drugs. However, the in vivo therapeutic efficacy of pHLIP-modified dual pH-responsive liposomes has not been validated.
In this study, a novel DVar7 (DACEEQNOWARYLEWLFPTETLLLEL) peptide-based dual pH-responsive DOX-encapsulated liposome ([email protected]) was designed and evaluated for in vivo therapeutic efficacy. Compared to original pHLIP, the truncated Var7 peptide showed higher tumor targeting,32 thus the nanocarriers modified with Var7 could lead to an enhanced tumor delivery efficiency. Besides, DVar7, as a D-type peptide, is more stable in vivo than the previously used L-pHLIP, which can further ensure the drug delivery efficiency of the cargo in tumors. In addition, unlike most dual acid-responsive nanomaterials that require complicated technology to achieve, DVar7 modified liposomes can be obtained by simply incubating DSPE-DVar7 with traditional DOX-liposome. The composition of doxorubicin-loaded dual pH-sensitive liposomes and their action after intravenous administration are shown in Figure 1. In the end, the therapeutic efficacy of dual pH-responsive liposome [email protected] was evaluated in breast cancer mouse model, and the effect of pH adjustment by glucose injection on the anticancer efficacy of dual pH-responsive liposomes was further assessed.
Figure 1 Preparation of [email protected] and its anticancer mechanism. [email protected] was prepared by coating doxorubicin with DOPE-liposomes and modifying [email protected] with DVar7. In the tumor acidic microenvironment, DVar7 folded and formed the alpha helix and inserted into the cell membrane, increasing the retention of liposomes in tumor and promoting the fusion of liposome with the cell membrane. Liposomes that were endocytosed into tumor cells quickly released doxorubicin upon the strongly acidic conditions of the lysosome. Therefore, doxorubicin could achieve a high concentration inside tumor cells during a short time, and then enter the nucleus to kill tumor cells.
Materials and Methods
1.2-Dioleoyl-sn-glycero-3-phosphoethanolamine (DOPE), 1.2-Dioleoyl-sn-glycero-3-phosphocholine (DOPC), and cholesterol and cholesteryl hemisuccinate (CHEMS) were purchased from A.V.T. (Shanghai, China). 1.2-Distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-2000] (DSPE-PEG2000) was purchased from NOF Corporation (Tokyo, Japan). DSPE-PEG2000-MAL was purchased from Xi’an ruixi Biological Technology (Xi’an, China). HEPES, EDTA·2Na·2H2O and doxycycline hyclate (DOX·HCl) were supplied by Sigma-Aldrich (Shanghai, China). DVar7 D(ACEEQNOWARYLEWLFPTETLLLEL) was synthesized by GL Biochem (Shanghai, China). LysoTracker Red was purchased from Shanghai Yeasen Biotech (Shanghai, China). The other chemicals and reagents were analytical grade.
It has been reported that highly metastatic tumor cells, such as MDA-MB-231 and MDA-MB-435, have a lower pHe than non-metastatic MCF-7 tumors of the same size.35 Therefore, MDA-MB-435S cell was chose as the positive cell line. Hela cell line was selected as a control cell line to prove that the uptake of acid-sensitive nanoparticles at different pH in cell experiments in vitro is mainly related to pH changes, and has nothing to do with cell types. The MDA-MB-435S and HeLa cells were purchased from American Type Culture Collection (ATCC, Manassas, VA, USA) and maintained under standard conditions according to ATCC. Fetal bovine serum, Leibovitz’s L15 medium, DMEM, trypsin, and penicillin-streptomycin solution were obtained from M&C Gene Technology (Beijing, China). MDA-MB-435S cells were cultured in Leibovitz’s L15 medium with 10% fetal bovine serum and 1% penicillin streptomycin combination and kept at 37 °C without CO2. HeLa cells were cultured in DMEM with 10% fetal bovine serum and 1% penicillin streptomycin combination and kept at 37 °C under 5% CO2. The cells were harvested with trypsin, and the cell suspension was used for experiments.
All animal experiments were performed in accordance with the guidelines of Peking University Health Science Center Animal Care and Use Committee. The subcutaneous MDA-MB-435S mouse model was established by subcutaneous injection of 5 × 106 cells into the right front flank of female nude mice (~15 g, BABL/c). The mice were used for imaging studies when the tumor volume reached approximately 200 ~ 300 mm3 (3–4 weeks after inoculation). The mice were used for the therapeutic experiment when the tumor volume reached approximately 50–100 mm3 (~2 weeks after inoculation). All animal experimental protocols were approved by Peking University Health Science Center Animal Care and Use Committee.
Synthesis of DSPE-PEG2000-DVar7
DSPE-PEG2000-DVar7 was synthesized by the covalent conjugation of DSPE-PEG2000-maleimide with the single cysteine residue at the N-terminus of DVar7. Briefly, DSPE-PEG2000-MAL 3.53 mg (~1.2 μmol) was dissolved in chloroform and evaporated to form a thin film in a round flask. The film was hydrated with HBS solution (pH 7.0) for 20 min and sonicated at 37 °C for 5 min. After DVar7 3.065 mg (~1 μmol) was added to the mixture and oscillated until completely dissolved, the mixture was separated by the reversed-phase high-performance liquid chromatography (HPLC) system. A Sepax Bio-C4 column (10 × 250 mm) was used for DSPE-PEG2000-DVar7 purification with a flow rate of 3 mL/min. For analytical HPLC, a Sepax Bio-C4 (4.6 × 250 mm) was used with a flow rate of 1 mL/min. The monitor wavelength was 254 nm, and the injection volume was 20 µL. The mobile phase was changed from 60% solvent A (0.1% trifluoroacetic acid [TFA] in water) and 40% solvent B (0.1% TFA in acetonitrile [ACN]) (0–5 min) to 20% solvent A and 80% solvent B at 15 min, followed by a gradient mobile phase from 0% solvent A and 100% solvent B at 35 min to 60% solvent A and 40% solvent B at 40 min. The existence of the product was ensured by SELDI-TOF mass-spectrometry analysis.
Preparation and Characterization of Liposomes
Both pH-responsive PEGylated liposomes (pSPL) and non-pH-responsive liposomes (nSPL) were prepared using a thin-film hydration method. Firstly, we prepared fluorescent liposomes [email protected] The detailed composition of fluorescent liposomes used in the study is given in Table 1. A chloroform solution of the desired lipid mixture (~20 μmol) without DSPE-PEG2000-DVar7 was vortexed and evaporated to form a thin film in a round flask equipped with a rotary evaporator at 37 °C under aspirator vacuum, continuing to evaporate for 5 min to remove residual organic solvent. Then, the film was hydrated with 1 mL of HBS solution (10 mM HEPES, 150 mM NaCl, pH 8.0) at 37 °C for 20 min to form multicellular vesicles (MLVs). MLVs were subjected to a miniature ultrasonic probe for 10 min (ultrasound 1 s and pause 1 s) to form small, unilamellar vesicles. The [email protected] was prepared by mixing 2% mol percentage of DSPE-PEG2000-DVar7 with fluorescent liposomes [email protected] at 55 °C for 1 h. Liposomes were sterilized by filtering through a 0.2 μm Millipore filter into a sterile vial and stored at 4 °C for in vitro and in vivo experiments.
Table 1 Formulation of Cy5.5-Loaded Liposomes
DOX-loaded pSPL and nSPL were prepared by the thin-film hydration method followed by the transmembrane pH gradient method. The detailed composition of DOX-loaded liposomes used in the study is shown in Table 2. The blank liposome suspensions were prepared by the same procedure as fluorescent liposomes. While the film of [email protected] was hydrated with 1.5 mL 0.25 mol/L (NH4)2SO4 (pH 5.23), the films of [email protected] and [email protected] were hydrated with 1.5 mL 0.25 mol/L (NH4)2SO4 (pH 7.0). The blank liposome suspension of [email protected] was eluted using Sephadex G-25 (PD-10 desalting column) pre-equilibrated with HBS solution (10 mM HEPES, 150 mM NaCl, pH 7.8) to form a pH gradient. DOX at pH 7.8 with a ratio of 1:10 (w/w, DOX/lipids) was introduced into the liposome suspension at 37 °C for 1 h, and an excess of free DOX was removed by washing with HBS solution. The blank liposome suspensions of [email protected] and [email protected] were prepared by the same procedure as the PB solution (pH 9.0) to replace the HBS solution. The [email protected] was prepared by mixing 2% mol percentage of DSPE-PEG2000-DVar7 with DOX-loaded liposomes [email protected] at 55 °C for 1 h. Liposomes were sterilized by filtering through a 0.2 μm Millipore filter into a sterile vial and stored at 4 °C for in vitro and in vivo experiments.
Table 2 Formulation of DOX-Loaded Liposomes
Characterization of Liposomes
The size, PDI, and zeta potential of the samples were measured using a Malvern Zetasizer (Brookhaven Instruments, Holtsville, NY) at 25 °C based on the principles of dynamic light scattering (DLS). Samples were typically 200 nmol liposomes in 1 mL of HBS solution (10 mM HEPES, 150 mM NaCl, pH 8.0).
The morphology of liposomes was observed using a transmission electron microscope (TecnaiG220, FEI, Hillsboro, OR, USA). The liposomal solution was dropped onto a carbon-coated copper grid followed by drying in air, and the sample was then subjected to observation.
Encapsulation Efficiency (EE) and Loading Efficiency (LE)
To determine encapsulation efficiency (%EE) and loading efficiency (%LE), firstly, the standard curve of DOX was drawn. The DOX solution was diluted to eight different concentrations with 5, 10, 15, 20, 25, 30, 40, and 50 μg/mL. Using the ultrapure water as blank control. The excitation wavelength of microplate reader was set at 480 nm, and the absorbance values of DOX solutions with different concentrations were measured. The standard curve of absorbance and concentration was drawn. The standard equation of DOX absorbance(y) and concentration(x) was y = 0.0222x, and the correlation coefficient R2 was 0.9998, indicating that there was a good linear relationship between DOX concentration and absorbance value in the range of 0–50 μg/mL.
The procedure in detail as follows: After doxorubicin encapsulation was completed, take two copies of 200 μL DOX loaded liposome solution, one of which was adjusted to 500 μL with buffer, then added 1 mL acidic isopropanol for demulsification, and react on the oscillator for 10 min. The blank control was 500 μL HBS buffer, added with 1 mL acidic isopropanol. Then, took 100 μL samples each and added them to the 96-well plate. The wavelength of the microplate reader SH-9000 (Corona Electric, Ibaraki, Japan) was set at 480 nm. Measure the absorbance and calculate the doxorubicin content. Passing the other copy through P-10 column, eluting with HBS buffer solution with pH 7.8, collecting the liposome part, and using buffer solution to increase the volume to 500 μL, after demulsification, measuring the absorbance value with microplate reader, and calculating the DOX content, which represents the DOX content loaded by liposomes.
EE was calculated as the amount of drug loaded in the liposomes divided by the initial amount of the drug. Encapsulation efficiency (%EE) = Amount of drug loaded in liposomes/Amount of drug added × 100%. LE was calculated as the molar ratio of the drug loaded into liposomes to the total of lipids. Loading efficiency (%LE) = Amount of drug in liposomes/Amount of liposomes × 100%. The encapsulation efficiency (%EE) of [email protected], [email protected], [email protected] were 98%, 90%, and 93%, respectively. The loading efficiency (%LE) of [email protected], [email protected], [email protected] was 9.8%, 9.0%, and 9.3%, respectively.
In vitro Stability and Acid Sensitivity
The physicochemical stability of liposomes was investigated over 30 days. Liposomes were stored at 4 °C and room temperature. Particle size and distribution of liposomes were measured on day 0, day 7 and day 30. The leakage rate of DOX liposomes was monitored with an enzyme standard instrument after separation and purification by a PD-10 column. The acid sensitivity of liposomes was assessed by measuring particle size changes after the liposomes were incubated with different pH solutions for an hour.
In vitro Drug Release of DOX Liposomes
The DOX release rates from liposomes with different pH values were investigated using a dialysis method. Briefly, 1 mL of DOX-loaded liposomes was transferred to a dialysis bag (MWCO 35000 Da, Beijing Solarbio Science & Technology Co., Ltd. Beijing, China) and then dialyzed against 40 mL of release medium with different pH in a tube and placed in a shaking incubator at 37 °C. One milliliter of media was removed at 1, 2, 4, 8, 24, 48 h, and an equivalent volume of fresh media was added at the same time. The amount of released DOX was determined using the multiscan spectrum with an excitation wavelength of 480 nm. The last time point result was used to calculate the DOX release rate.
The in vitro cellular uptake of Cy5.5 fluorescent liposomes was evaluated in MDA-MB-435S cancer cells and HeLa cancer cells. Briefly, the cells were seeded at a density of 2×104 per well in glass bottom cell culture dishes and incubated for 24 h at 37 °C. Then, 100 μL fluorescent liposomes (at a final Cy5.5 concentration of 20 μM) with different pH values (6.0 and 7.4) was added and incubated for 1 h. The cells were washed twice with ice-cold PBS and further analyzed by a FACSCalibur system. CLSM was used to study the cellular uptake and intracellular release behaviors of DOX-loaded liposomes in MDA-MB-435S. Briefly, the cells were seeded at a density of 2×104 per well in glass bottom cell culture dishes and incubated for 24 h at 37 °C. Then, 100 μL of free DOX or DOX-loaded liposomes with different pH values was added and incubated for 1 h. The cells were washed twice with ice-cold PBS. The cell nuclei were stained with 100 μL of Hoechst 33342 (1 μg/mL), and lysosomes were stained with LysoTracker Red for 20 min. After washing with PBS three times, the fluorescence images were captured by a TCS-NT confocal microscope (Wetzler, Heidelberg, Germany). The fluorescence intensity of DOX in cells was analyzed by using ImageJ software.
In vitro Cytotoxicity
First, we used flow cytometry to determine the change in doxorubicin liposome uptake with incubation time and determined the optimal drug action time of the MTT experiment was 4 h. Briefly, co-incubated doxorubicin liposomes (the final concentration was 20 µg/mL) and 1 mL MDA-MB-435S tumor cells (2×106/mL) for 1, 2, 4, or 8 h, and then the cells were washed with PBS three times. Flow cytometry was performed to determine the changes in doxorubicin fluorescence intensity in the cell with time. The cytotoxicity of blank lipids and DOX-loaded liposomes in MDA-MB-435S cells was evaluated by MTT assay. The cells were plated in a 96-well plate (1×104 cells/well) and incubated at 37 °C in an atmosphere containing 5% CO2 overnight. Then, the cell culture media was replaced with fresh media with different pH values containing blank lipids, DOX.HCl, or DOX-loaded liposomes with different concentrations and incubated for 4 h. Then, the medium was replaced with fresh medium of the corresponding pH and cultured for 48 h. The nontreated cells were used as negative controls. After 48 h, the medium was replaced by a mixture of 100 μL of fresh medium and 20 μL of MTT. After incubating for 1 h, the absorbance was determined at 490 nm by a microplate reader. The cell viability was estimated, and IC50 values were calculated using GraphPad Prism software (GraphPad Software, Inc., La Jolla, CA, USA).
In vivo Tumor Targeting
MDA-MB-435S cells (5×106 per mouse) were subcutaneously injected into the right flank of the mice. When the tumor size reached 200–300 mm3, tumor-bearing mice were intravenously injected with 100 μL liposomes ([email protected], [email protected], [email protected], n = 3, the amount of Cy5.5 was 10 nmol). The last group received a high concentration glucose injection 45 min before the [email protected] liposomes injection. Fluorescence images were acquired by an IVIS Spectrum imaging system at 4, 24, 48, and 72 h post-injection. The excitation filter was 675 nm, and the emission filter was 723 nm. The fluorescence signals of the tumor and the contralateral thigh were recorded using the IVIS Spectrum imaging system for quantification. The results were statistically analyzed using GraphPad Prism software (GraphPad Software, Inc., La Jolla, CA, USA).
In vivo Antitumor Efficacy
For the tumor suppression study, MDA-MB-435S cells (5×106 per mouse) were subcutaneously injected into the right flank of the mice. When the tumor size reached 50–100 mm3, these mice were divided into seven groups (n = 6, mean tumor size was 63.5 mm3). After the preparation of liposomes, we have removed the free DOX by purification with PD-10 column and determined the encapsulation efficiency (EE), loading efficiency (LE), and final concentration of DOX in liposomes. Saline, free DOX, [email protected], [email protected], [email protected], [email protected] combined with glucose injection, or [email protected] combined with glucose injection was injected into the mice via the tail vein at a dose of 5 mg/kg of DOX equivalent. Before injection, DOX-loaded liposomes were diluted with PBS to the appropriate concentration to achieve an administration volume of about 100 μL. The injections were given every four days for a total of five times. The tumor sizes were measured by a calliper every other day after treatment. Tumor volume (V) was calculated by the following equation: V = AB2×0.5, where A was the longer and B was the shorter diameter (mm). The relative tumor volumes were normalized to their initial sizes. Meanwhile, body weight was calculated during the treatment period. At the end of treatment, the mice were sacrificed to collect tumors and heart, liver, spleen, lung, and kidney tissues for further analyses. The tumor weight was measured by a balance and analyzed statistically. Finally, the tumor and other tissues were used for the H&E staining.
For histological analysis, the tumors and other tissues were cut into 5 μm thick sections and stained with hematoxylin and eosin (H&E), and the sections were observed under an optical microscope.
Data are presented as the mean ± SEM. Differences between the groups were assessed by one-way ANOVA, and a P value less than 0.05 was considered significant.
Results and Discussion
Preparation and Characterization of Liposomes
The preparation of the dual pH-responsive drug-loaded lipid system can be divided into three steps: (i) preparation of DOPE liposomes; (ii) preparation of DOX-loaded DOPE liposomes; and (iii) modification DOX-loaded DOPE liposome with targeting molecule DSPE-PEG2000-DVar7. The targeting molecule DSPE-PEG2000-DVar7 was synthesized by coupling DSPE-PEG2000-MAL with DVar7, and the product was validated by mass spectrometry (Supplementary Figure S1). Polyethylene glycol (PEG) motif at 6% of molar ratio was introduced into liposomes through the insertion of DSPE-PEG2000 and DSPE-PEG2000-DVar7, which could not only keep liposomes stable and reduce the leakage of drugs during the circulation in blood but also reduce the nonspecific interaction between liposomes and serum proteins, thus preventing the clearance of liposomes in the reticular endothelial system (RES).36 Blank DOPE liposomes were prepared with DOPE, CHEMS, and DSPE-PEG2000 by the thin-film hydration method. Doxorubicin liposomes were prepared by pH gradient loading method.
Dynamic light scattering (DLS) analysis indicated that the hydrodynamic diameter of the liposomes was approximately 130 nm with a polydispersity index (PDI) of <0.2 (Figure 2A). The results of transmission electron microscopy indicated that the particle size of liposomes was approximately 130 nm (Figure 2B). Detailed nanoparticle characterizations of Cy5.5-loaded liposomes and DOX-loaded liposomes were provided in Supplementary Figure S2. The particle size of the Cy5.5-loaded liposomes remained stable for 30 days (Supplementary Figure S3). Ultraviolet (UV) absorption spectroscopy results showed that the maximum UV absorption wavelength of free DOX was 480 nm, and the maximum absorption wavelength of doxorubicin liposomes was 497 nm with a reduced redshift (Figure 2C), indicating the successful encapsulation of DOX. The encapsulation rate of DOX in the three liposomes was 98%, 90%, and 93%, respectively. The DOX-loaded liposomes had no significant change in particle size for 30 days at 4 °C and room temperature (Supplementary Figure S4), the PDIs were remain <0.2, and the drug leakage rates were less than 3%, indicating good stability.
In vitro Acid-Triggered Drug Release from Liposomes
In vitro acid-sensitivity was determined by measuring the particle size change under different pH conditions with DLS (Figure 2D). The particle size of [email protected] liposomes was barely changed along with the decrease of pH and remained at approximately 135 nm. With the decrease of pH, the particle size of [email protected] and [email protected] liposomes increased from 130 nm to 150 nm, which indicating that liposomes were acid-sensitive in vitro.
Afterward, to confirm that pH-responsive controlled drug release of liposomes, we measured the drug release of doxorubicin liposomes under different pH conditions by dialysis and obtained a drug release curve by measuring the concentration of DOX in the dialysis medium at different time points. The results were standardized with the release curve at pH 7.4, and the drug release rates of the three drug-carrying liposomes under different pH conditions were obtained (Figure 2E). With the decrease of pH, [email protected] at pH 5.3 released twice as much drug as at pH 7.4. The drug release of [email protected] increased significantly at pH 5.3, which was three times higher than at pH 7.4, reflecting the acid-sensitive drug release characteristics of DOPE lipid structure. Furthermore, [email protected] at pH 5.3 released nearly five times more drugs than at pH 7.4. This should be attributed to the structural change of DVar7, which was inserted into the phospholipid bilayer under acidic conditions, bringing the liposomes and cell membranes close to each other, thereby increasing the interaction, leading to the destruction of liposome structure, and increasing the drug release from the liposomes.34 These results confirmed that DOPE-liposomes were acid-sensitive and their increased release of DOX was triggered by an acidic environment. In addition, the presence of DVar7 further accelerated the release of DOX in acidic environment.
In vitro Cell Uptake
Since the cell uptake of pSPL and nSPL can be visually compared under confocal microscopy, we evaluated the cellular uptake behavior of fluorescent liposomes in HeLa and MDA-MB-435S cells (Supplementary Figure S5) and measured the fluorescence intensity of the cells to reflect the uptake of fluorescent liposomes. The fluorescence intensity was quantitatively analyzed with ImageJ software. As shown in Figure 3A and B, in the two cell lines, there was no significant difference in uptake between these three fluorescent liposomes at pH 7.4. However, at pH 6.0, compared with [email protected], the acid-sensitive [email protected] liposomes showed significantly increased uptake in tumor cells (MDA-MB-435S: 6.97 ± 0.01 vs 5.82 ±0.07, n = 3, ****p< 0.0001; HeLa: 7.40 ± 0.02 vs 5.82 ± 0.07, n = 3, ****p<0.0001). Compared with [email protected], the dual pH-responsive liposomes ([email protected]) showed further increased uptake in tumor cells (MDA-MB-435S: 7.55 ± 0.04 vs 6.97 ± 0.01, n = 3, ***p<0.001; HeLa: 7.75 ± 0.03 vs 7.40 ± 0.02, ***p<0.001). These results showed that dual acid-sensitive fluorescent liposomes had a notable advantage on increasing cell uptake at pH 6.0, and this was independent of cell types. For both two cell lines, tumor cell uptake of pSPL increased significantly under at pH 6.0 compared to pH 7.4.
MDA-MB-435S cells were used to evaluate the cell uptake of DOX-loaded liposomes in different pH conditions. As shown in Figure 3C and D, free DOX and [email protected] liposomes had no significant differences in uptake under different pH conditions. However, at pH 6.0, the cellular uptake of [email protected] and [email protected] was much higher than that at pH 7.4 ([email protected]: 3591.00 ± 38.92 vs 3157.00 ± 22.18, n = 3, ***p<0.001; [email protected]: 4671.00 ± 144.10 vs 3748.00 ± 109.80, n = 3, **p<0.01).
Next, the change of liposome uptake in tumor cells over time was evaluated. In the first three time points (1, 2, and 4 h), the cellular uptake of the three liposomes increased with time, and the change in uptake was not notable after 4 h. Thus, we believe that liposomes were mainly taken into the cells within the first 4 h and prolonged the incubation time will not further increase the uptake of liposomes (Supplementary Figure S6).
In vitro Cell Toxicity
To verify the therapeutic effect of liposomes in vitro, the toxicity of blank liposomes and DOX-loaded liposomes under different pH conditions was determined by MTT assay. After tumor cells were co-incubated with blank phospholipid for 48 h, the cell survival rate remained above 90%, even though the phospholipid concentration was as high as 1000 nmol/mL (Supplementary Figure S7), which indicated the good biocompatibility of the liposomes. Free DOX and three DOX liposomes showed concentration-dependent cytotoxic effects on MDA-MB-435S (Figure 3E and F). Compared with free DOX, [email protected] had a weaker cytotoxic effect on cells, probably because DOX·HCl is a small molecule that plays a direct role after entering cells, while [email protected] releases DOX slowly after entering cells through endocytosis and cannot reach a high concentration quickly. The IC50 of [email protected] was 27.85 μg/mL at pH 7.4, which was slightly improved at pH 6.0 (24.09 μg/mL). This indicated that the extracellular pH 6.0 acidic microenvironment could not significantly improve the killing effect of monoacid-sensitive liposome [email protected] on tumor cells. After all, it is usually effective in lysosomes (pH 5.0).16–19 For the dual pH-responsive liposome [email protected], the IC50 values for pH 6.0 (16.37 μg/mL) were significantly improved than that of pH 7.4 (24.09 μg/mL), indicating that the cell-killing effect of dual pH-responsive liposomes was significantly enhanced at pH 6.0. The acidic microenvironment increases the pH gradient inside and outside the cells, so the DVar7 could be reconstructed and inserted itself into the cell membrane under acidic conditions to promote the fusion between liposomes and tumor cell membranes. The dual pH-responsive liposomes allowed more liposomes to enter tumor cells and release doxorubicin rapidly. This led to a high concentration of drug inside tumor cells, and the achievement of the better anticancer effect.
Small Animal in vivo Fluorescence Imaging
As a truncated pHLIP, Var7 has better overall water solubility compared to full-length WT-pHLIP, and more appropriate for imaging purpose. Moreover, DVar7 can reduce degradation by enzymes, remain stable in vivo to respond to acidic microenvironments. We have previously used DVar7 for tumor imaging studies, and the results showed that DVar7 is still acid-sensitive, and the SPECT imaging with 99mTc-labeled DVar7 can clearly visualize the acidic tumors.37 Here, to study the in vivo behaviors of DOX-liposomes, the near-infrared fluorescent dye Cy5.5 was encapsulated into liposomes (Cy5.5-liposomes) for fluorescence imaging in tumor-bearing animals. Near-infrared fluorescence imaging was performed at 4, 24, 48, and 72 h after injection of three fluorescent liposomes, and another group of mice was injected with high-concentration glucose 45 min before administration of [email protected] liposomes (Figure 4A). The fluorescence intensity of the tumor sites was quantitatively analyzed and normalized with the contralateral hind leg muscles as a background (Figure 4B–D). Compared with the DOPC-lip, DOPE-lip had higher accumulation in the tumors at 4 and 24 h (4 h: 0.72 ± 0.01 vs 1.12 ± 0.03, 24 h: 0.84 ±0.02 vs 1.23 ± 0.05, n = 3, **p<0.01, ***p<0.001). The DOPE-DVar7-lip showed higher tumor uptake than DOPE-lip at 48 h and 72 h (48 h: 1.21 ± 0.06 vs 0.83 ± 0.07, 72 h: 1.06 ± 0.01 vs 0.60 ± 0.06, n = 3, *p<0.05, **p<0.01). For the group of DOPE-DVar7-lip with the injection of high concentration of glucose, the pH of the tumor microenvironment was acidified, which significantly increased tumor uptake than the DOPE-DVar7-lip treatment alone at 4 h (1.93 ± 0.08 vs 1.22 ± 0.07, n = 3, **p<0.01), and the high uptake lasted until 72 h after administration (48 h: 1.47 ± 0.06 vs 1.21 ± 0.06, 72 h: 1.51 ± 0.01 vs 1.06 ± 0.01, n = 3. *p<0.05, ***p<0.001). Near-infrared fluorescence imaging experiments demonstrated the tumor-targeting advantages of dual pH-responsive liposomes.
Figure 4 In vivo tumor-targeting ability. (A) Representative fluorescence images of MDA-MB-435S tumor-bearing BALB/c mice at 4, 24, 48, and 72 h after intravenous injection with [email protected], [email protected], [email protected], and [email protected] plus glucose injection. (B–D) Fluorescence intensity of the Cy5.5 signal between groups of [email protected] and [email protected] (B), [email protected] and [email protected] (C), [email protected] and [email protected] plus glucose injection (D) (mean ± SEM, n = 3, *p < 0.05, **p < 0.01, ***p < 0.001).
Previous studies have shown that the injection of glucose can modestly increase the pH gradient inside and outside tumor cells. Forty-five minutes after injection of glucose, the pH gradient of tumor cells can turn to 0.61, with a pHe of 6.5.38–40 In this study, the tumor delivery efficiency of dual pH-responsive liposomes was further enhanced by regulating the tumor microenvironment with glucose injection.
Dual pH-Responsive DOX Liposome for Tumor-Targeted Therapy
The anticancer effect of the doxorubicin liposome was evaluated in a mouse model subcutaneously inoculated with MDA-MB-435S cells. There was a significant difference between the free doxorubicin and the [email protected] group on the 11th day of treatment, with tumor volumes of 196.10 ± 17.06 mm3 vs 154.50 ± 6.35 mm3 (*p<0.05), respectively (Figure 5A). Compared with free doxorubicin, the long-circulating DOX liposome avoided direct contact between doxorubicin and the extracellular acidic microenvironment, reduced the loss of DOX in the extracellular environment and its distribution in normal tissues and organs. Therefore, the therapeutic effect was improved. The significant difference in tumor volume between the [email protected] group and the [email protected] group appeared on 4th day (102.00 ± 4.72 mm3 vs 73.40 ± 4.83 mm3, *p<0.05). The [email protected] group and the [email protected] group were significantly different, with tumor volumes of 116.50 ± 9.22 mm3 vs 86.73 ± 6.51 mm3 (*p<0.05) on the 15th day of treatment. The [email protected] group and the acidified microenvironment [email protected] group showed a significant difference on the 3rd day of treatment, with volumes of 73.69 ± 5.48 mm3 vs 52.31 ± 4.95 mm3 (*p<0.05). There was no significant difference in the [email protected] groups with or without acidified microenvironment throughout the treatment, indicating that the pH of the tumor microenvironment had no effect on the efficacy of non-acid-responsive liposomes and that glucose injection itself has no therapeutic effect. During the entire treatment period, the body weight of all groups fluctuated slightly, and no weight loss exceeded 20% (Figure S8). At the end of the treatment, we excised and collected the tumor tissues of mice (Figure 5B) and compared the difference between the tumor weights of the groups (Figure 5C). As a result, the [email protected] group showed the best therapeutic efficacy (n = 6), adding glucose to increase the acidity of the tumor microenvironment significantly improved the curative effect. The mouse tumor tissue and organs, including heart, liver, spleen, lung, and kidney, were stained with H&E to observe histopathological changes. As shown in Figure S9, there were no morphological changes in the heart, liver, spleen, lung, and kidney of each group, which indicated that the dose of the drug used in the experiment was non-toxic. By comparing the H&E staining results of the tumors (Figure 5D), the [email protected], [email protected] and [email protected]+glucose treatment groups had notable tumor necrosis. Among them, the tumor necrosis of the [email protected]+glucose treatment group was the most severe, indicating that it had the best tumor suppressive efficacy.41
Figure 5 Antitumor effect in vivo. Saline, free DOX, [email protected], [email protected], [email protected], a combination of glucose and [email protected], and a combination of glucose and [email protected] were administered to MDA-MB-435S tumor-bearing mice via tail vein injections every 4 days at a DOX dose of 10 mg/kg. Saline was used as a negative control, and the injection volume was 0.1 mL. The treatment of glucose was given 45 minutes after liposome injection. (A) Tumor volume changes of MDA-MB-435S tumor-bearing mice. (n = 6, *p<0.05). (B) Picture of tumor tissues collected from MDA-MB-435S tumor-bearing mice on day 24. (C) A comparison of the final tumor weights of different groups was performed on 24th day (mean ± SEM, n = 6, *p<0.05, **p<0.01, ***p<0.001). (D) H&E analysis of tumor tissues.
Tumor drug resistance is one of the main reasons for the failure of chemotherapy and molecularly targeted drug therapy.42,43 Low extracellular pH (pHe) in tumor cells creates an ion-trapping phenomenon known as a physiological drug barrier that inhibits the use of weak base chemotherapeutic drugs.38,44–46 Because a lot of chemotherapy drugs are alkaline, the clinical effect of chemotherapy is greatly affected. Here, we prepared the dual pH-responsive liposomes to take advantage of the nature of the acidic tumor microenvironment. Compared with traditional liposomes, the dual pH-responsive liposomes have remarkable advantages in tumor targeted treatment and overcoming doxorubicin resistance. Moreover, the glucose injection, which acidified the tumor microenvironment, further improved the therapeutic effect. The combination of dual pH-responsive liposomes and pH adjustment provides ideas for clinical optimization of therapeutic liposomes and has great potential for clinical improvement of drug resistance.47 Since MDA-MB-435S is not a highly malignant tumor model, if it is replaced with a more malignant tumor model, dual pH-responsive liposomes may be able to show more therapeutic advantages.48 Studies have found that, besides injecting high concentrations of glucose, the tumor microenvironment can also be acidified by heating the tumor site. Further research is needed to determine which method is more effective in tumor treatment.
In summary, a novel dual pH-responsive DOX-encapsulated liposome was prepared, and a solution to enhance the therapeutic effect of pH-responsive liposomes by regulating the pH value of tumor microenvironment was provided. In the acidic tumor microenvironment, the acid-sensitive peptide DVar7 was allosterically inserted into the tumor cell membrane, which enhanced the tumor uptake of liposomes and prolonged the retention time of liposomes in tumors. At the same time, through acid-sensitive DOPE, acid-controlled release of DOX in lysosomes of tumor cells was accelerated. Therefore, the dual pH-responsive DOX-encapsulated liposome [email protected] showed significantly enhanced treatment efficacy than traditional liposomes and mono pH-responsive liposomes. In addition, regulating the pH value of TME by injecting the clinically implementable glucose could further improve the therapeutic effect of the dual pH-responsive liposomes, which possesses great potential for improving drug resistance in clinical practice.
This research was supported by National Natural Science Foundation of China (NSFC) projects (81630045, 81971676, 81571727, and 81927802), and Strategic Priority Research Program of the Chinese Academy of Sciences (XDA12020110), the Youth Innovation Promotion Association of Chinese Academy of Sciences (YIPACAS) project (YIPA2016090).
The authors declared no financial or nonfinancial conflicts of interest for this work.
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