Antitumor Effects of Self-Assembling Peptide-Emodin in situ Hydrogels in vitro and in vivo
Authors Wei W, Tang J, Li H, Huang Y, Yin C, Li D, Tang F
Received 17 September 2020
Accepted for publication 21 December 2020
Published 6 January 2021 Volume 2021:16 Pages 47—60
Checked for plagiarism Yes
Review by Single anonymous peer review
Peer reviewer comments 3
Editor who approved publication: Dr Yan Shen
Weipeng Wei,1– 3,* Jianhua Tang,4,* Hongfang Li,1– 3 Yongsheng Huang,5 Chengchen Yin,1– 3 Dan Li,6 Fushan Tang1– 3
1Department of Clinical Pharmacy, Key Laboratory of Basic Pharmacology of Guizhou Province and School of Pharmacy, Zunyi Medical University, Zunyi 563000, People’s Republic of China; 2Key Laboratory of Basic Pharmacology of Ministry of Education and Joint International Research Laboratory of Ethnomedicine of Ministry of Education, Zunyi Medical University, Zunyi 563000, People’s Republic of China; 3Key Laboratory of Clinical Pharmacy of Zunyi City, Zunyi Medical University, Zunyi 563000, People’s Republic of China; 4Cancer Research UK Manchester Institute, The University of Manchester, Cheshire SK10 4TG, UK; 5Peking Union Medical College, Chinese Academy of Medical Sciences, Institute of Basic Medical Sciences, Beijing 100005, People’s Republic of China; 6State Key Laboratory of Molecular Oncology, National Cancer Center/National Clinical Research Center for Cancer/Cancer Hospital, Chinese Academy of Medical Sciences and Peking Union Medical College, Beijing 100021, People’s Republic of China
*These authors contributed equally to this work
Correspondence: Fushan Tang
Department of Clinical Pharmacy, School of Pharmacy, Zunyi Medical University, Guizhou, People’s Republic of China
Tel +86851 28642337
Fax +86851 28642334
Email [email protected]
Cancer Hospital, Chinese Academy of Medical Sciences, Beijing, People’s Republic of China
Tel +8610 87787107
Email [email protected]
Purpose: To study the in vitro and in vivo antitumor effects of the colloidal suspension-in situ hydrogel of emodin (EM) constructed with the self-assembling peptide RADA16-I and systematically evaluate the feasibility of the delivery system.
Methods: The MTT and colony-formation assays were used to determine the viability of normal cells NCTC 1469 and tumor cells Hepa1-6. The uptake of EM in the RADA16-I-EM in situ hydrogel by tumor cells was analyzed by laser confocal microscope and flow cytometry. Flow cytometry was used to detect the cell apoptosis and cell cycle distribution. Transwell assay was used to detect the migration and invasion of tumor cells. The antitumor efficacy of the RADA16-I-EM in situ hydrogel and its toxic effects was further assessed in vivo on Hepa1-6 tumor-bearing C57 mice.
Results: The results showed that the RADA16-I-EM in situ hydrogels could obviously reduce the toxicity of EM to normal cells and the survival of tumor cells. The uptake of EM by the cells from the hydrogels was obviously increased and could significantly induce apoptosis and arrest cell cycle in the G2/M phase, and reduce the migration, invasion and clone-formation ability of the cells. The RADA16-I-EM in situ hydrogel could also effectively inhibit the tumor growth and obviously decrease the toxic effects of EM on normal tissues in vivo.
Conclusion: Our results demonstrated that RADA16-I has the potential to be a carrier for the hydrophobic drug EM and can effectively improve the delivery of hydrophobic antitumor drugs with enhanced antitumor effects and reduced toxic effects of the drugs on normal cells and tissues.
Keywords: self-assembling peptide, emodin, in situ hydrogels, antitumor, drug delivery system
Tumors are malignant diseases that seriously affect human health, and chemotherapy is inevitably needed by most patients.1–3 Traditional chemotherapy often requires increased dosages and prolonged administration time to achieve the expected therapeutic effect, which will often increase drug toxicity and side effects.4 At present, the clinical use of most antitumor drugs is still challenged by the low bioavailability caused by poor water solubility and inability to accumulate at the tumor site. However, the poor selectivity of drugs and toxicity and side effects caused by the addition of corresponding excipients or solvents in the dosage form have limited the clinical use of many antitumor drugs to a certain extent.5–7
Emodin (EM) is a natural anthraquinone compound with promising antibacterial, blood microcirculation-promoting and antitumor effects.8–10 It was reported that EM can produce considerable toxicity to a variety of tumor cells.11–15 However, the poor solubility and ease of crystal precipitation of EM in water have resulted in difficulties associated with the injection administration.16,17 Most of the studies that examined novel drug delivery systems of EM, such as liposomes and nanoparticles, were unsuccessful because of low drug loading and cumbersome preparation processes of the dosage form.18,19
The injectable hydrogels can be used to effectively circumvent systemic side effects of traditional intravenous chemotherapy by locally releasing drugs at the tumor site.20,21 Based on different tumor types and stages, a variety of hydrogel drug delivery systems have been developed.22–27 Hydrogels are in an injectable solution, suspension or semi-solid state before administration and semi-solid or solid hydrogels can immediately form in situ at the site of drug administration through phase transition stimulated by external conditions (light, temperature, pH, etc.).28–31 After the direct injection of the drug-loaded colloidal suspensions or solutions at the tumor site, the hydrogels can form in situ, and the drug loaded in the hydrogels can be mainly concentrated in the tumor tissue with improved therapeutic effects on tumors and reduced toxic effects of drugs on normal organs.32–38
Ionic complementary self-assembling peptides are structurally composed by alternately arranging positively and negatively charged amino acids with hydrophobic amino acids and can spontaneously assemble under the action of electrostatic forces and hydrophobic interactions.20,39 With the hydrophilic amino acids in the structure, including positively charged arginine (Arg, R) and negatively charged aspartic acid (Asp, D) at neutral pH, and the hydrophobic amino acid as the non-polar amino acid alanine (Ala, A), the most typical ionic complementary self-assembling peptide, RADA16-I, has been believed and demonstrated that the hydrophobic regions of its high-level structure can encapsulate hydrophobic drugs, while the hydrophilic regions can maintain the stability of the system in aqueous solutions.40–43
We previously developed hydrophobic drug-loaded RADA16-I suspension-in situ hydrogels.44,45 In this study, the antitumor effects of EM-loaded RADA16-I suspension-in situ hydrogels were systematically evaluated in vitro and in vivo. A new hydrophobic drug administration form is expected to be developed by strengthening research on self-assembling peptides as drug carrier materials.
Materials and Methods
Raw EM materials (batch no. FY1175S0310) with an EM purity ≥98% were purchased from Nantong Feiyu Biotechnology Co., Ltd. (Jiangsu, China). High-glucose Dulbecco’s Modified Eagle’s Medium (DMEM) and 1% antibiotics (100× streptomycin-penicillin) were purchased from HyClone Inc. (Logan, UT, USA). The 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyltetrazolium bromide (MTT) and phosphate-buffered saline (PBS) were purchased from Beijing Solarbio Technology Co., Ltd. (Beijing, China). Dimethyl sulfoxide (DMSO) was purchased from Beijing Dingguo Changsheng Biotechnology Co., Ltd. (Beijing, China). Foetal bovine serum (FBS) was purchased from Gibco (Thermo Fisher Scientific, Inc., Waltham, MA, USA). Trypsin-EDTA solution (0.25%) was purchased from Biosharp Inc. (Shanghai, China). Heparin sodium (MFCD00081689) was purchased from Shanghai Yuanye Biological Technology Co., Ltd. (Shanghai, China). 4ʹ,6-Diamidino-2-phenylindole (DAPI) was purchased from Beijing Pulilai Gene Biotechnology Co., Ltd. (Beijing, China). Crystal violet was purchased from Shenyang Shengda Chemical Co., Ltd. (Shenyang, China). A BD PharmingenTM cell cycle kit was purchased from BD Bioscience (Shanghai, China). An Annexin V-Alexa Fluor 647/PI apoptosis detection kit was purchased from Beijing Jinpulai Biotechnology Co., Ltd. (Beijing, China). PEG400 was purchased from Sinopharm Group Chemical Reagent Co., Ltd. (Beijing, China). Formaldehyde was purchased from Jiangsu Haixing Chemical Co., Ltd. (Jiangsu, China). Haematoxylin (BA-4097) and eosin (BA-4099) (H&E) were purchased from Zhuhai Besso Biotechnology Co., Ltd. (Zhuhai, China). A TUNEL kit from Roche (30967400) was purchased from the Swiss Roche Group (Shanxi, China). The nuclear antigen Ki-67 was purchased from Wuxi Aurui Dongyuan Biotechnology Co., Ltd. (Wuxi, China). Male SPF-grade C57 mice weighing 18~20 g (experimental unit licence number: SYXK (Qian) 2014–003; experimental animal licence number: SCXK (Beijing) 2016–0002) were purchased from Speyford Biotechnology Co., Ltd. (Beijing, China). Animal experiments were conducted in accordance with the European Community guidelines (European Convention for the Protection of Spinal Cord Animals for Experimental and Other Scientific Purposes) and approved by the Institutional Animal Care and Use Committee of Zunyi Medical University (Approval number: ZMUER2014-2-069). NCTC 1469 normal mouse liver cells were purchased from Nanjing Saihongrui Biotechnology Co., Ltd. (Nanjing, China). Hepa1-6 mouse liver cancer cells were purchased from Shanghai Fuheng Biotechnology Co., Ltd. (Shanghai, China). Cell culture bottles and other related consumables were purchased from Corning, Inc. (Corning, NY, USA). All experimental protocols were performed in accordance with the relevant guidelines.
The self-assembling peptide RADA16-I (1712.77 g/mol) was commercially synthesized by Shanghai Biotech Bioscience & Technology Co., Ltd. (Shanghai, China). The peptide comprises the amino acid sequence n-RADARADARADARADA-c for RADA16-I. The N-and C-termini of the peptides were protected by acetyl and amino groups, respectively.
NCTC 1469 and Hepa1-6 cells were cultured in DMEM (Gibco) supplemented with 10% FBS (Gibco), penicillin (100 U/mL), and streptomycin (100 μg/mL). The cells were incubated in a humidified atmosphere of 5% CO2 at 37°C.
Analysis of Haemolytic Properties
Haemoglobin was used as an indicator of haemolysis, that is, red blood cell damage. A haemolysis evaluation of the effects of non-drug-loaded RADA16-I was conducted, and the percentage of haemolysis was determined by comparison with a 100% haemolytic sample. Heparinized rabbit blood was collected, and a 2% erythrocyte suspension was prepared. The suspension was added to Eppendorf tubes, and RADA16-I samples at concentrations of 1.0, 3.0, 5.0, 7.0, and 9.0 mg/mL were added to the tubes. PBS and H2O were used as negative and positive controls, respectively. Then, the Eppendorf tubes were incubated in a 37°C constant temperature water bath for 3 h. The tubes were then centrifuged at 3000 rpm/min for 5 min. A full-wavelength scan of the positive control tube was measured using a UV-Vis spectrophotometer to determine the maximum absorption peak of haemoglobin. Supernatant absorption was then measured using the sample tubes at this wavelength. The percentage of haemolysis (%H) was calculated according to the following formula:
%H = (D1-D2)/(D3-D2) × 100%
where D1 is the average absorbance of the test sample, and D2 and D3 are the absorbances of the negative and positive controls, respectively.
Investigation of Hydrogel Formation by a RADA16-I-EM Suspension
The self-assembling peptide RADA16-I-EM colloidal suspension was prepared by the magnetic stirring method, added into in vitro systems (PBS, 0.9% NaCl, or cell culture media) mimicking in vivo conditions, and injected para-tumorally or intra-tumorally to investigate the formation of hydrogels.
Cell Viability Assay
NCTC 1469 and Hepa1-6 cells were plated onto 96-well plates (4000 cells per well) in DMEM with 10% FBS in the presence of RADA16-I (0.5, 1.0, 2.0, 4.0, and 6.0 mg/mL), EM (60, 80, 100, 120, 140, 160, 180, and 200 μM), or RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL, and concentrations of EM were 60, 80, 100, 120, 140, 160, 180, and 200 μM). DMEM served as the blank, and untreated cells served as controls. Cells were incubated for 24 and 72 h at 37°C with 5% CO2. An MTT solution was prepared at 5 mg/mL in PBS and filtered through a 0.2-μm filter. MTT (20 μL/well) was added to each well. Cells were further incubated with MTT at 37°C for 4 h. Then, the spent medium was discarded, DMSO (150 μL/well) was added to each well, and the plate was further shaken for 10 min at room temperature. Finally, the absorbance of each well was measured at 490 nm using a microplate reader (Bio-Rad Laboratories, Hercules, CA, USA) to determine the OD values. The cell viability was calculated using the following calculation:
Cell survival rate (%) = (OD1-OD2)/(OD3-OD2) × 100%
where OD1 is the absorbance of the sample, OD2 is the absorbance of the blank, and OD3 is the absorbance of the control.
In vitro Fluorescence Imaging
Cellular uptake of free EM and RADA16-I-EM hydrogels was evaluated by imaging the cells under a confocal laser scanning microscope (Leica, Wetzlar, Germany). The procedure used for the preparation of the cell samples was as follows. Hepa1-6 cells were cultured in DMEM on a special Petri dish for laser confocal microscopy at a suitable concentration of cells per dish. After growth overnight, the cells were treated with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL, and the final concentrations of EM were 120, 160, and 200 μM) and incubated for 24 h. The culture medium was discarded, and the cells were washed with PBS and then fixed for 30 min in 4% paraformaldehyde. The fixed cells were then washed with PBS three times to remove excess paraformaldehyde, and their nuclei were stained with DAPI.
Cellular Uptake of EM via Flow Cytometry
Cellular uptake of EM from free EM and RADA16-I-EM hydrogels was also studied by flow cytometry (Becton-Dickinson, San Jose, CA, USA). The procedure used to prepare the cell samples was as follows. Hepa1-6 cells were cultured in DMEM on a 6-well plate at a suitable concentration of cells per well. After growth overnight, the cells were treated with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL and the concentrations of EM were 120, 160, and 200 μM) and incubated for 24 h. The culture medium was discarded, and the cells were washed with ice-cold PBS followed by the addition of trypsin to detach the cells from the plate; then, the cells were re-suspended in 300 μL of PBS to obtain single cells.
Annexin V/PI Staining Assay for Apoptosis
A cell apoptosis study was performed with Hepa1-6 cells using an Annexin V-Alexa Fluor 647/PI double staining assay kit supplied by BD Biosciences, China. In brief, cells were cultured (60-mm dish at 37°C) and then treated separately with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL, and the concentrations of EM were 120, 160, and 200 μM) for 24 h. The cells were then collected and washed with ice-cold PBS, stained with Annexin V-Alexa Fluor 647 and PI for 15 min at room temperature in the dark according to the manufacturer’s protocol, and analysed by using flow cytometry (Becton-Dickinson, San Jose, CA, USA) to examine the apoptotic cell numbers.
Cell Cycle Detection Assay
Hepa1-6 cells were seeded in six-well plates. After incubation for 24 h, the cells were treated with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL and the concentrations of EM were 120, 160, and 200 μM) for 24 h in complete medium. The cells were then collected by trypsinization and washed with ice-cold PBS. The cells were fixed with ice-cold 75% ethanol (v/v) overnight at −20°C; the samples were then centrifuged, washed with ice-cold PBS, and stained with propidium iodide (PI, 50 μg/mL) for 30 min at 37°C in the dark according to the manufacturer’s instructions. Finally, the samples were analysed by flow cytometry (Becton-Dickinson, San Jose, CA, USA), and the percentage of cell cycle cells was calculated according to the number of cells in the respective phase.
Invasion and Migration Assays
Migration and invasion studies were conducted using a Transwell plate that was coated with (for invasion) or without (for migration) Matrigel matrix (BD Biosciences, Bedford, MA). Hepa1-6 cells were cultured (60-mm dish at 37°C) and then treated separately with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL, and the concentrations of EM were 120, 160, and 200 μM) for 24 h. The cells were then collected and washed with PBS. After preparing cell suspensions in serum-free DMEM containing 1 × 105 cells, the cells were then seeded into the upper chamber, and 700 μL DMEM with 20% FBS was added to each well under the chambers. After culturing for 18 h at 37°C and 5% CO2, cells that migrated or invaded through the membrane were fixed with methanol for 15 min and then stained with a 2.0% crystal violet-methanol solution for 15 min. Finally, invasive and migrated cell numbers were visualized by fluorescence microscopy and counted.
For the colony-formation assay, Hepa1-6 cells were cultured (60-mm dish at 37°C) and then treated separately with free EM and RADA16-I-EM hydrogels (in which the concentration of RADA16-I was 5.0 mg/mL, and the concentrations of EM were 120, 160, and 200 μM) for 24 h. The cells were collected and washed with PBS. Cells were seeded in six-well plates at a concentration of 800 cells per well containing DMEM with 10% FBS, and the culture medium was replaced with a complete medium every 72 h. The cells were incubated at 37°C and 5% CO2 for 8 days. After 8 days, the cells were washed with PBS, fixed with methanol for 15 min, and stained with a 2.0% crystal violet-methanol solution for 15 min. The six-well plates were washed with water and dried at room temperature. The colonies were visualized using a gel imager and counted.
In vivo Antitumor Efficacy and Immunohistology
For the in vivo therapeutic efficacy of the RADA16-I-EM hydrogel, C57 mice bearing Hepa1-6 cells were randomly divided into four groups (n=8 per group) when the tumors reached a size of approximately 150–250 mm3. PBS served as a negative control. The experimental groups included non-drug-loaded RADA16-I hydrogel, free EM (10.0 mg/kg per dose), and RADA16-I-EM hydrogels (at an equivalent dose of 10.0 mg/kg EM per dose). The animals were injected with 50 μL of the control or experimental group dose via intra-tumor injection every 2 days. The tumor diameters (mm) and body weight (g) were monitored before each dosing regimen seven times for a total of 14 days. The mice were sacrificed by cervical vertebral dislocation after 14 days, and their tumor tissues were dissected and weighed, and fixed in a 10% formaldehyde solution. The lungs, heart, kidneys, liver, and spleen were also collected and fixed in a 10% formaldehyde solution. In the histological assay, tumor and organ tissues were fixed with a 10% formaldehyde solution for 48 h at 4°C, and tissue sections were stained with H&E for microscopic observation. Apoptosis of cells in tumor tissues following treatments was evaluated using the TUNEL assay according to the manufacturer’s instructions. For analysis of cell proliferation, Ki-67 immunohistochemical staining was applied according to the manufacturer’s instructions. The tumor volumes were measured by the following formula:
Tumor volume (V) = (tumor width)2 × tumor length/2
Statistical analysis was performed using SPSS 18.0 statistical software. All the obtained data are presented as the mean ± SD. Comparison between two groups was statistically evaluated by Student’s t-test; multiple comparisons were statistically evaluated by the one-way ANOVA with the LSD-t or the Dunnett-t-test. A probability (P) less than 0.05 was considered statistically significant.
Results and Discussion
In vitro Haemocompatibility and Cytocompatibility of RADA16-I
Haemocompatibility and cytocompatibility are two important factors considering biomaterial applications.46,47 The results of the haemolysis experiment showed that the 2.0% erythrocyte suspension was completely ruptured in H2O (the hypotonic solution), but haemolysis did not occur in PBS (the isotonic solution) or the RADA16-I solution (Figure 1Aⅰ). A full-wavelength scan of the positive control supernatant (H2O) showed that haemoglobin had a maximum absorption peak at 542 nm, while neither the PBS nor RADA16-I solutions had absorption peaks at this wavelength (Figure 1Aⅱ). The supernatant of each experimental group containing a peptide solution was tested for absorbance at 542 nm; the calculated RADA16-I concentration was 1.0–9.0 mg/mL, and the haemolysis rate was less than 5.0% (Figure 1Aⅲ). According to previous reports, materials with a haemolysis rate of less than 5% are considered safe materials meeting the requirements of biomaterials and medical devices for haemolysis experiments.48,49 Taken together, RADA16-I has good blood compatibility in this concentration range.
The cytotoxicity of RADA16-I on cells (Hepa1-6 and NCTC 1469) was detected using the MTT assay to evaluate the cell compatibility of RADA16-I. The cytotoxicity results showed that with the increasing RADA16-I concentration and incubation time, the inhibitory effects of RADA16-I on the proliferation of cancer cells and normal cells were not significant, and the final cell viabilities were both greater than 80% (Figure 1B), which was indicative of the zero-grade and I-grade ranges according to the cytotoxicity evaluation standard, therefore meeting the cytotoxicity requirements of the pharmacopoeia evaluation of biological materials. The above experimental results preliminarily showed that the self-assembling peptide RADA16-I hydrogel is biologically safe and has the potential to be a drug delivery carrier.
Hydrogel Formation of the RADA16-I-EM Suspension
As shown in Figure 2, the results of the hydrogel formation showed that the RADA16-I-EM colloidal suspension can immediately form three-dimensional hydrogels in situ, in buffer solutions in vitro, and in para-/intra-tumor tissues in vivo, and the hydrogels were resistant to dispersal to some extent.
Figure 2 Formation of RADA16-I-EM suspension-in situ hydrogel system.
In vitro Cell Viabilities
EM and its derivatives possess anticancer activity against various tumors, including liver and lung tumors.12,13 Here, the antitumor efficiency of the RADA16-I-EM suspension was evaluated using the MTT assay and Hepa1-6 liver cancer cells. The toxic effects of EM on normal cells (NCTC 1469) were also analysed by the MTT assay after the drug was encapsulated in RADA16-I. The EM in water suspension (free EM) and RADA16-I-EM hydrogels both obviously inhibited the proliferation of Hepa1-6 cells within 24–72 h. With the increase of the incubation time and dose, the antiproliferative effects of free EM and RADA16-I-EM hydrogels on Hepa1-6 cells increased notably, but the antiproliferative effects of RADA16-I-EM hydrogels were significantly greater than that of the free EM, particularly after 72 h of incubation (P<0.05, Figure 3). For NCTC 1469 cells, both free EM and RADA16-I-EM hydrogels had certain inhibitory effects on proliferation; however, the inhibitory effect of RADA16-I-EM hydrogels on normal cells was significantly less than that of free EM (P<0.05, Figure 3). This phenomenon may be related to the slow release of EM into the cells, controlled by RADA16-I-EM hydrogels that formed in situ, resulting in an inability to immediately reach the minimum toxic concentration of the drug, thus causing less damage to normal cells. It was concluded that the self-assembling peptide RADA16-I can effectively control the release of EM, prolong the inhibitory effect of EM on the growth of Hepa1-6 liver cancer cells in vitro, and reduce the toxic effect of EM on normal cells.
In vitro Cellular Uptake
Whether the encapsulated drugs are successfully released and taken up by cells is the key point for evaluating drug-loaded nanogels and their chemotherapeutic agents.50,51 In this study, laser confocal microscopy and flow cytometry were employed to explore the cellular uptake of nanoparticles. As shown in Figure 4A, after the cells were incubated for 24 h with the drugs, the cytoplasmic distribution of the green fluorescence of EM in cells of the RADA16-I-EM in situ hydrogels group was significantly greater than that of free EM. The results of quantitative detection by flow cytometry showed similar results. As shown in Figure 4B, as the concentration of EM increased, the amount of EM detected in the cells also increased, but the amount of EM entering the cells from the RADA16-I-EM in situ hydrogels was significantly greater than that from the free EM (P<0.01). The cellular uptake of EM from RADA16-I-EM in situ hydrogels dramatically increased compared with that from the free EM. Considering that the main difference between free EM and RADA16-I-EM was the introduction of RADA16-I in the EM suspension (RADA16-I-EM), it is reasonable to speculate that RADA16-I plays an important role in the improvement of the solubility of hydrophobic drugs as well as their anticancer performance.
Evaluation of Cell Apoptosis
It has been cumulatively documented that EM causes cell growth inhibition via an apoptotic mechanism.52,53 In the current work, Hepa1-6 cells were employed to investigate the apoptotic process caused by free EM and RADA16-I-EM hydrogels. As shown in Figure 5, untreated Hepa1-6 cells showed little apoptosis and necrosis (early apoptosis: ~2.4%, late apoptosis: ~2.9%, and necrosis: ~1.1%); when the final concentration of EM reached 200 μM, free EM led to increases in both cellular apoptosis and necrosis: ~3.3% early apoptosis, ~18.2% late apoptosis, and ~10.2% necrosis. The death of cells treated with RADA16-I-EM hydrogels changed dramatically with ~1.3% early apoptosis, ~28.6% late apoptosis and ~23.2% necrosis. Compared with the blank control, RADA16-I hydrogels without EM had little effect on early apoptosis, late apoptosis or necrosis in cells. The results clearly showed that EM loaded in RADA16-I assembly produced a superior anticancer effect to that of EM alone through the enhanced induction of cancer cell apoptosis.
Examination of Cell Cycle Distribution
To further investigate the mechanism underlying EM-induced tumor cell proliferation inhibition, we analysed the effect of free EM and RADA16-I-EM hydrogels on cell cycle distribution by flow cytometry. As shown in Figure 6, compared with untreated Hepa1-6 cells, an accumulation of cells in the G2/M phase from ~13.89% to ~49.77% was observed when Hepa1-6 cells were treated with a final EM concentration of 200 μM. Simultaneously, the cell fractions in the S and G0/G1 phases decreased from ~41.09% and ~45.02% to ~32.24% and ~17.99%, respectively. In addition, compared with free EM, RADA16-I-EM hydrogels led to significant cell cycle arrest, in which the cell accumulation of the G2/M phase increased from ~14.51% to ~55.33%, and the cell fraction of the S and G0/G1 phases dramatically decreased from ~44.00% and ~41.49% to ~23.20% and ~21.47%, respectively. Taken together, it was demonstrated that EM induces G2/M arrest in liver cancer cells and that RADA16-I-EM in situ hydrogels block G2/M phase arrest more significantly than EM alone.
In vitro Cell Migration, Invasion, and Cloning Capabilities
The Transwell and clone-formation assays were applied to elucidate the effects of EM in the free EM and the RADA16-I-EM in situ hydrogels on the migration, invasion, and proliferation of Hepa1-6 cells. The cells in RADA16-I-EM in situ hydrogel group showed lower levels of membrane penetration and clone formation than those in the free EM group. Using the Transwell system, we verified that RADA16-I-EM in situ hydrogels reduced the migration and invasion ability of Hepa1-6 cells. As shown in Figure 7A, both free EM and RADA16-I-EM in situ hydrogels effectively inhibited the migration and invasion of Hepa1-6 cells compared with untreated cells and cells treated with empty vector RADA16-I. In addition, RADA16-I-EM in situ hydrogels had stronger inhibition effects on cell migration and invasion than free EM. The clone-formation assays revealed that free EM and RADA16-I-EM in situ hydrogels attenuated the colony-forming ability of Hepa1-6 cells compared with untreated cells and cells treated with empty vector RADA16-I (Figure 7B), while RADA16-I-EM in situ hydrogels reduced the colony-forming ability of Hepa1-6 cells more significantly than free EM. Based on the migration, invasion and proliferation assays, we concluded that the self-assembling peptide RADA16-I can stabilize the EM in aqueous solutions and achieve a slow-release effect, which can increase the cellular uptake of EM from the RADA16-I-EM in situ hydrogels by tumor cells to inhibit the migration, invasion and cloning formation of tumor cells more significantly, thereby enhancing the antitumor effects of EM on tumor cells.
In vivo Studies in Hepa1-6 Tumor-Bearing Mice
To further investigate the potential of RADA16-I-EM in situ hydrogels for cancer treatment in vivo, Hepa1-6 tumor-bearing mouse models were treated with free EM and RADA16-I-EM hydrogels via intra-tumor injection (Figure 8A and B). As shown in Figure 8C, the weight of mice in each group did not change significantly after 14 days of administration. The tumors in mice treated with PBS and RADA16-I grew rapidly, but tumor growth in mice treated with free EM and RADA16-I-EM hydrogels was effectively inhibited (Figure 8D). In particular, the inhibition effects of RADA16-I-EM in situ hydrogels were more obvious than those of free EM, and the powerful antitumor activity of RADA16-I-EM in situ hydrogels was primarily attributed to the efficient release of EM from RADA16-I-EM hydrogels, which allowed for better antitumor effects. Strikingly, both tumor size and tumor weight decreased significantly after the Hepa1-6 tumor-bearing mice were systematically treated with the RADA16-I-EM in situ hydrogel system (Figure 8E and F), indicating the effective therapeutic efficacy of the RADA16-I-EM in situ hydrogel formulation in vivo.
Major of the H&E stained sections of tumor tissues in the PBS and RADA16-I groups showed excessive cell proliferation and obvious nuclear polymorphisms. Tumor-bearing mice treated by free EM and RADA16-I-EM hydrogels exhibited reduced tumor cells and enhanced levels of tumor necrosis in the H&E-stained sections of tumor tissues; however, the RADA16-I-EM hydrogels group showed the fewest tumor cells and the highest level of tumor necrosis among all the groups (Figure 9A). Immunohistochemical analysis was performed to detect the expression of TUNEL-positive cells in tumor tissues (Figure 9B). The TUNEL assay, which was used to assess tumor apoptosis, also confirmed that treatment with the RADA16-I-EM in situ hydrogels induced more significant levels of apoptosis than that in other groups, implying the relatively high antitumor activity of the RADA16-I-EM hydrogels compared with free EM. Consistent with the results obtained from the H&E and TUNEL staining assays, the Ki-67 staining assay also demonstrated that RADA16-I-EM hydrogel treatment significantly reduced the percentage of Ki67-positive cells proliferation to a higher extent than any other group (Figure 9D). The levels of cells proliferation in tumor after treatment were also evaluated (Figure 9C and E). There was a high level of TUNEL-positive cells and lower Ki67-positive cells in tumor after treatment with EMS and RADA16-I-EM, especially in the RADA16-I-EM in situ hydrogels, with a significant statistical difference from other groups. These results together demonstrated that RADA16-I-EM in situ hydrogels could significantly improve antitumor effects. Moreover, no significant body weight loss was recorded in the mice in any group during the 14 days of treatment (Figure 8A). In addition, systemic toxicity to major organs (heart, liver, spleen, lungs, and kidneys) was investigated by H&E staining (Figure 10), and the results strongly suggested low systemic toxicity and the minimum side effects of the RADA16-I-EM in situ hydrogel formulation.
Figure 10 H&E staining of main organs (heart, liver, spleen, lungs, and kidneys) from Hepa1-6 tumor-bearing mice on the 14th day of treatment. “↗” represents the toxic site of the organs tissue during the drug EM administration.
EM can be effectively loaded into the suspension formed under mechanical stirring with the self-assembling peptide RADA16-I in water, and the suspension can form hydrogels in situ, in buffer solutions in vitro, and in para-/intra-tumor tissues in vivo. The RADA16-I-EM in situ hydrogels can effectively improve the proliferation-inhibiting effects on Hepa1-6 liver tumor cells and reduce the toxic effects on normal cells of EM in vitro. Furthermore, the RADA16-I-EM in situ hydrogels can significantly reduce the tumor growth rate and reduce the toxic side effects of EM on normal organs in vivo compared with the free EM in subcutaneously implanted murine Hepa1-6 liver tumor models, which was primarily attributed to the RADA16-I-EM hydrogels effectively delivering EM into the tumor tissue. Hence, this study demonstrated that the suspension-in situ hydrogels constructed with the self-assembling peptide RADA16-I can be used as a promising nanoplatform for stabilized hydrophobic drug administration and a localized sustained drug delivery system in biomedicine, highlighting their potential in further clinical applications.
This work was supported by the National Natural Science Foundation of China (NO: 31460246), Beijing Nova Program (xx2018040), the Guizhou Provincial Science and Technology Foundation (NO: Qiankehe LH  7564), the Project of Special Funds for Science and Technology Cooperation in Guizhou Provinces and Zunyi City (Shengshikehe  53), Talents Training Project Fund of Zunyi City “15581 Talents Elite Project” (NO: 31460246).
The authors have declared no competing interests in this work.
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