Treatment of breast cancer with autophagy inhibitory microRNAs carried by AGO2-conjugated nanoparticles
Journal of Nanobiotechnology volume 18, Article number: 65 (2020)
Nanoparticle based gene delivery systems holds great promise. Superparamagnetic iron oxide nanoparticles (SPIONs) are being heavily investigated due to good biocompatibility and added diagnostic potential, rendering such nanoparticles theranostic. Yet, commonly used cationic coatings for efficient delivery of such anionic cargos, results in significant toxicity limiting translation of the technology to the clinic. Here, we describe a highly biocompatible, small and non-cationic SPION-based theranostic nanoparticles as novel gene therapy agents. We propose for the first-time, the usage of the microRNA machinery RISC complex component Argonaute 2 (AGO2) protein as a microRNA stabilizing agent and a delivery vehicle. In this study, AGO2 protein-conjugated, anti-HER2 antibody-linked and fluorophore-tagged SPION nanoparticles were developed (SP-AH nanoparticles) and used as a carrier for an autophagy inhibitory microRNA, MIR376B. These functionalized nanoparticles selectively delivered an effective amount of the microRNA into HER2-positive breast cancer cell lines in vitro and in a xenograft nude mice model of breast cancer in vivo, and successfully blocked autophagy. Furthermore, combination of the chemotherapy agent cisplatin with MIR376B-loaded SP-AH nanoparticles increased the efficacy of the anti-cancer treatment both in vitro in cells and in vivo in the nude mice. Therefore, we propose that AGO2 protein conjugated SPIONs are a new class of theranostic nanoparticles and can be efficiently used as innovative, non-cationic, non-toxic gene therapy tools for targeted therapy of cancer.
Most human diseases are caused by abnormalities and malfunction of genes and proteins. Hence, gene therapy of diseases has been considered as an alternative treatment approach in the last decades. A major limitation in gene therapy is related to the choice of gene delivery vehicle. Viral vectors used as a general vehicle in many of the studies suffer from a number of adverse reactions and side-effects, including immune reactions against carrier viruses and mutagenesis related to the viral genomic integrations etc. [1,2,3]. Nanoparticles emerge as alternative and safer gene delivery vehicle candidates. A wide range of cationic polymers, i.e. polyethylene imine (PEI) , cationic dendrimers , polymeric nanoparticles, i.e. Chitosan/poly (lactide-co-glycolide) (PLGA) , lipid derivatives , collagen derivatives , and inorganic nanoparticles with cationic coatings such as silica nanoparticles , gold nanoparticles (Au NPs)  were tested both in in vitro and in vivo models of diseases as alternative gene delivery vehicles. Cationic polymers offer a large number of functionalities which allow high loading capacity, co-delivery of other therapeutic agents, attachment of targeting ligands. However, these systems are generally toxic to cells and tissues, limiting their dosage and applications. Moreover, they lack the imaging modality which would provide tremendous advantages in the monitoring of delivery, disease progress and therapy. From this perspective, designing inorganic nanoparticles with diagnostic modality as gene delivery vehicles offers an immense potential.
Superparamagnetic iron oxide (Fe2O3) nanoparticles (SPIONs, SP) were widely used in the core of various gene delivery systems. SPIONs are biocompatible and non-toxic and they have been commonly used as FDA-approved magnetic resonance imaging contrast agents . They can also be manipulated, targeted and heated using an external magnetic field, making them ideal candidates for theranostic medical applications, including gene therapy [12,13,14,15,16,17].
Suitable coating materials over the crystalline iron oxide core are required to allow binding to nucleic acids. Such coatings need to be cationic, e.g. PEI , chitosan , PAMAM dendrimer , since the nucleic acid cargo is anionic. Toxicity of the cationic polymers, non-specific uptake and immune reactions, might be observed due to positive charges on these delivery agents and limit their successful usage in the clinic [21, 22]. Furthermore, improvement of selectivity of the delivery vehicle is critical in order to enhance the therapeutic effect while reducing the side effects. Targeting may be achieved through attachment of ligands, such as peptides, proteins or small molecules that selectively recognize target cells and improve internalization. Moreover, nanoparticles should be small enough to escape from the reticuloendothelial system (RES, including mononuclear phagocyte system of liver and spleen). Hence, there is an urgent need for non-toxic, small, target specific and theranostic nanoparticles, allowing efficient nucleic acid binding and delivery as well as medical imaging simultaneously.
Various nucleic acid molecules, e.g. DNA, RNA, modified nucleotides, are being utilized in gene therapy attempts. MicroRNAs (miRNAs) are small (18–21 nucleotide), protein non-coding, endogenous RNA molecules that regulate key biological events, including cell proliferation, differentiation and survival. MiRNAs modulate cellular levels and translation of dozens of messenger RNAs, controlling abundance of their protein products . By this way, they determine cellular responses to various stimuli under physiological and pathological conditions. Indeed, dysregulation, i.e. upregulation or downregulation, of several miRNAs was observed in a wide variety of health problems, including cancer .
To date, more than 2000 miRNAs were described in the human genome. MicroRNA genes were found in both intergenic or intragenic gene loci. Following RNA polymerase II-dependent transcription, maturation of miRNA precursors is processed by several protein complexes that are found in the nucleus and the cytosol .
Resulting mature miRNA duplexes are eventually loaded onto the RNA-induced silencing complexes (RISC) in the cytosol. Argonaute (AGO) proteins are key components of the RISC. They bind to single-stranded mature microRNAs, guiding them to their target messenger RNAs (mRNAs), and leading to mRNA degradation or translation blockage . Moreover, AGO proteins contribute to the stability of mature miRNA strands in RNAse containing biological environments. Indeed, cell- or vesicle-free and stable mature miRNAs were found in complex with AGO proteins in the blood circulation [27,28,29,30]. In vitro tests confirmed that AGO2 increase the stability of these small RNAs [31,32,33,34,35].
Recent studies showed that miRNAs tightly regulate autophagy, an evolutionarily conserved cellular stress response mechanism . For example, we have previously showed that MIR376B blocked excessive cellular autophagy through targeting of its key components BECN1 and ATG4C [36, 37]. Autophagy was shown to support survival of cells that are exposed to stressful conditions, including chemotherapy agents. Consequently, in established tumors, combination of autophagy blocking agents and chemotherapy drugs resulted in more efficient tumor elimination than single agent treatments [38,39,40].
Here, inspired by the stability of naturally occurring AGO protein/miRNA complexes in the blood circulation, we have designed AGO2 conjugated SPIONs as tumor targeted miRNA delivery vehicles for gene therapy of cancer. As the initial target, we have studied breast cancer as a model and developed AGO2 protein conjugated SPIONs (SP-A) and used HER2 antibodies as targeting moieties. Addition of a fluorescent tag on the antibody allowed optical detection of the particles in vitro and in vivo (SP-AH nanoparticles). SP-AH were successfully synthesized from poly(acrylic acid)-coated SPIONs with excellent colloidal stability and in small sizes. This is the first example to AGO2 protein containing nanoparticles and the first demonstration of AGO2/nanoparticle conjugate as a transfection agent.
Autophagy inhibiting MIR376B miRNAs were selectively delivered into HER2-positive breast cancer cell lines (SKBR3 and MDA-MB-453) by SP-AH nanoparticles. Effective inhibition of autophagic activity by nanoparticles was demonstrated in vitro in cells and in vivo xenograft model of breast cancer. Furthermore, we showed that combination of MIR376B-loaded SP-AH nanoparticles with chemotherapy drug cisplatin, significantly potentiated the tumor response to therapy both in vitro and in vivo. Therefore, we introduce the AGO2 protein as a powerful and stable miRNA carrier component for non-cationic, nanoparticle-based gene delivery approaches.
Results and discussion
Characterization of AGO2 as a miRNA stabilizer protein
Previous reports indicated that cell-free miRNAs were found in blood circulation in complex with the AGO2 protein that increased their stability [31, 32]. In order to confirm these observations, we have overexpressed the AGO2 protein, performed immunoprecipitation assays and tested the amount of bound miRNA using qPCR. AGO2 overexpression led to six times increase in the amount of protein-bound endogenous mammalian MIR376B levels compared to control (Additional file 1: Fig. S1a, b). In order to determine the effect of AGO2 on miRNA stability, we have incubated immunoprecipitates for 21 days at room temperature. Even after this incubation period, a significant amount of miRNA was still detected by qPCR, indicating that AGO2 protein bound miRNAs were protected from degradation (Additional file 1: Fig. S1c). These results indicated that AGO2 protein may be used as a miRNA binding and stabilizing tool in gene therapy.
Synthesis and characterization of AGO2 conjugated and anti-HER2 labeled SPIONs (SP-AH)
Since synthesis of small colloidal SPIONs requires relatively high reaction temperature and basic condition as well as large excess of the coating molecule, first highly functional and stable poly(acrylic acid) coated SPIONs (SP) were prepared and then conjugated with the recombinant full length AGO2 protein as a nucleic acid binding component (Fig. 1). Poly(acrylic acid) coated SPIONs (SP) were synthesized via an aqueous co-precipitation of ferric and ferrous salts under alkaline conditions (Fig. 1a). TEM micrograph shows small crystalline cores of nearly 4 nm without a noticeable aggregation (Fig. 2a and Additional file 1: Fig. S7a). EDX analysis further demonstrated Fe and O composition of SPIONs (Additional file 1: Fig. S7a). Small size and colloidal stability of SP were also confirmed with 17 nm hydrodynamic size (number average) measured by DLS and strong negative surface charge, − 19 meV (Fig. 2b and Additional file 1: Fig. S2a). XRD diffraction patterns of SP nanoparticles belong to the iron oxide spinel structure of magnetite (Fe3O4) (Fig. 2b). Broadening in the peaks is attributed to the nanometer size of powder analyte. SP showed no hysteresis when subjected to magnetization–demagnetization cycle indicating the superparamagnetic nature of these nanoparticles (Fig. 2c). Thermogravimetric analysis (TGA) of SP showed a two-stage degradation similar to pure PAA and the PAA content of SP was determined as 36% by weight (Fig. 2c). Presence of the poly(acrylic acid) (PAA) coating on SPION core was confirmed with the strong symmetric stretching band of carbonyl (1570 cm−1) and broad band of hydroxyl groups (2800–3700 cm−1) representing the –COOH functionality of PAA in the FTIR spectrum of the SP (Fig. 2d and Additional file 1: Fig. S2d). In all later conjugation reactions performed on these SP, this PAA content was used as the basis of stoichiometry.
Recombinant full length AGO2 protein was covalently attached to –COOH groups of SP via direct amide bond using the two step EDC/NHS chemistry producing the AGO2-conjugated SPIONs (SP-A) (Fig. 1c). AGO2 content of the SP-A was calculated spectroscopically using the Bradford Assay (Additional file 1: Fig. S3a), as 5.5 µg AGO2 per mg of nanoparticles.
In order to target nanoparticles to HER2-positive breast cancer cells, these nanoparticles were tagged with fluorescent dye labeled anti-HER2 antibody using a 39.7 Å PEG spacer. This strategy aims to protrude the anti-HER2 from the bulk of the nanoparticle coating (PAA and AGO2) for effective interaction of anti-HER2 with the cell surface receptor. First, maleimide functional SP prepared via direct amidation of SP with maleimide-PEG-NH2. For the conjugation, the anti-HER2 antibody was thiolated using the Traut’s reagent. Nearly 55 sulfhydryl units were calculated per anti-HER2 with the Ellman’s test. Then, thiolated anti-HER2 was coupled with the maleimide functional SP via thiol-ene chemistry (Fig. 1d). For the optical tracking of nanoparticles, and confirmation of anti-HER2 conjugation to SP-A, antibody was labelled with a far-red fluorophore (Dylight650) (Fig. 1b). This strategy also placed the fluorescent tag away from the SPION core which is a strong absorber in the visible region, maximizing the intensity of the dye for optical detection. The fluorophore tag and hence the amount of anti-HER2 antibody on SP-AH nanoparticles were quantified from the luminescence intensity of the dye at 672 nm as nearly 0.8 mol of dye per mole of antibody and 24 anti-HER2 per particle (Additional file 1: Fig. S3b, c). Protein conjugations to SP was confirmed by the appearance of amide peaks in FTIR (Fig. 2d) and specific Dot-blot (Fig. 2e) analysis. Ability to detect the fluorescently labeled SP-AH by IVIS imaging system was confirmed before the animal studies and compared with non-fluorescent SP (Fig. 2f).
SP conjugated only with anti-HER2 antibody (SP-H) or only with the fluorophore (SP-F) as well as fluorophore-labeled AGO2 conjugated nanoparticles (SP-AF) were also prepared as control nanoparticles to be used in targeting and miRNA binding assays. The fluorophore on SP-F and SP-AF nanoparticles were determined from the fluorescence intensity of the dye at 672 nm (Additional file 1: Fig. S3d, e). Particle properties including the hydrodynamic size (nm), poly dispersity indexes (PDI), zeta potential (mV) as well as composition of each nanoparticle are summarized in Table 1. One very important point to notice here is the small size of the target particle SP-AH which is 50 nm and zeta potential which is − 24 mV. The synthetic approach was designed to guarantee the small size to prevent fast clearance from the blood stream. Commonly used gene delivery systems are generally cationic, limiting their biocompatibility and increasing their toxicity. Negative surface charge of AGO2-conjugated nanoparticles is another novelty of this nanoparticle designed for gene delivery.
Investigation of biocompatibility and potential side-effects of SP-AH nanoparticles
In order to confirm biocompatibility, we treated MCF-7, SKBR3 or MDA-MB-453 breast cancer cells with increasing concentrations (5–500 µg/ml; for 48 h) of SP-AH or control SP nanoparticles and evaluated cell survival in vitro. No significant difference in cell viability was observed even at the highest concentration of nanoparticles. Neither SP-AH nor SP were toxic to cells after 48 h of treatment (Additional file 1: Fig. S4). Next, SP-AH or SP nanoparticles were i.v. injected to mice through tail vein. No significant change in body weight was observed in nanoparticle injected mice compared to age-matched PBS injected mice after 10 or 40 days of follow-up (Additional file 1: Fig. S4b). Moreover, blood biochemistry and complete blood count showed no prominent difference between the SP-AH and SP nanoparticles versus PBS injected mice at 10 and even 40 days after the injection (Additional file 1: Tables S1 and S2). Histopathology analyses of the major organs of these mice did not reveal any abnormality (Additional file 1: Fig. S4c). In addition, the iron content of various organs, including liver, spleen and kidney, of SP-AH administered mice determined by inductively coupled plasma (ICP) showed no difference between PBS- and nanoparticle-injected mice, indicating that SP-AH nanoparticles were metabolized and did not accumulate in the tissues (Fig. 5a). Therefore, we concluded that nanoparticles used in this study are biocompatible at a cellular and organismal level both in short- and long-term tests.
Targeting of HER2-positive breast cancer cells by SP-AH nanoparticles
HER2/NEU/ERBB2 is a member of the epidermal growth factor receptor family and 10–30% of breast tumors are HER2 positive . We first determined the HER2 expression levels of three different breast cancer-derived cell lines. Dot blot analysis using an anti-HER2 antibody revealed that highest expression of the receptor was observed in MDA-MB-453 and SKBR3 cells, while MCF-7 cells were low expressors (Fig. 3a). Next cells were treated with PBS control or fluorophore-labeled SP-F, SP-AF or SP-AH nanoparticles and FACScan analyses were performed. While fluorescent signal obtained from SP-F and SP-AF-treated cells were at the auto-fluorescence level of control cells, there was a clear signal-shift proportional to the HER2 expression levels of cells when treated with SP-AH nanoparticles, indicating successful receptor-mediated targeting of MDA-MB-453 and SKBR3 cells with anti-HER2-conjugated SP-AH (Fig. 3b). Confocal microscopy analysis results were in line with FACScan results. SKBR3 and MDA-MB-453 cell membranes were brightly stained with SP-AH nanoparticles, yet, no signal was observed in HER2 low expressor MCF-7 cells or cells treated with SP-F nanoparticles devoid of HER2 antibody (Fig. 3c).
In order to assess receptor-mediated uptake kinetics and cellular destination of SP-AH nanoparticles, SKBR3 and MDA cells were treated with SP-AH nanoparticles and fluorescent signals were followed at various time points. Cellular targeting of nanoparticles (150 μg/ml NPs; 5 min, 1 h (h), 6 h, 24 h and 48 h) was observed after 1 h, and the total signal intensity gradually increased over time (Fig. 3d, e). Especially at early time points, MDA cells that are high expressors of the HER2 receptor showed a stronger fluorescence signal, indicative of higher nanoparticle accumulation compared to SKBR3 cells (Fig. 3e). We also checked colocalization of nanoparticles with early (RAB5) and late (RAB9) endosomal markers (Fig. 3f). We could observe colocalization with early endosomes after 3 h and late endosomes after 6 h.
These results confirm that SP-AH nanoparticles targeted HER2-positive cells and were internalized in these cells through endocytosis.
Targeting of HER2-positive breast cancer xenograft tumors by SP-AH nanoparticles
To validate targeting of HER2-positive breast tumors with SP-AH nanoparticles in vivo in mice, we created xenograft tumors of SKBR3 or MDA-MB-453 cells. When the tumors reached around 50 mm3, 1 month after tumor cell subcutaneous xenograft, mice were i.v. injected with PBS or SP-AH nanoparticles. Whole body analysis of mice under an IVIS fluorescence imaging system showed that SP-AH nanoparticles specifically and selectively accumulated in xenograft tumors but not in other organs or tissues (Fig. 4a and Additional file 1: Fig. S5b). Confocal microscopy analysis of sections of tumor specimen further confirmed tumor targeting by SP-AH nanoparticles (Fig. 4b). Moreover, ICP analysis of tumor iron content provided another proof that iron-oxide nanoparticles selectively accumulated in SP-AH-injected tumors compared to PBS-injected controls (Additional file 1: Fig. S5a).
These results demonstrate that SP-AH nanoparticles successfully and selectively targeted HER2-positive tumors in mice. Importantly, SP-AH nanoparticles were not detected in other tissues and organs.
SP-AH-mediated delivery of MIR376B and suppression of autophagy in vitro
We have previously characterized MIR376B as an autophagy inhibitory microRNA. We showed that MIR376B directly targeted key autophagy genes BECN1 and ATG4C and limited uncontrolled autophagy activation under cellular stress conditions creating a gas-and-break model of autophagy control [36, 37]. In fact, autophagy seems to act as a chemotherapy resistance mechanism, and several independent studies reported that combination of autophagy inhibitors with chemotherapy increased the efficacy of treatment [42,43,44]. Hence, inhibition of autophagy by MIR376B should potentiate chemotherapy-induced cell death. In an effort of using SP-AH as a miRNA delivery agent, first the conditions of loading synthetic miRNA mimics onto SP-AH nanoparticles were optimized and then the cellular outcomes were determined. MIR376B levels were increased by several folds following their SP-AH-mediated delivery into SKBR3 (Fig. 5a) and MDA (Fig. 5f) cells. SP-H nanoparticles that do not contain AGO2 protein were also incubated under similar conditions with the miRNA mimics, but no significant increase was observed in MIR376B levels in cells treated with these particles, confirming that AGO2 is the key component of the designed nanoparticle for miRNA delivery. Under these conditions, expression of MIR376B targets BECN1 and ATG4C were also analyzed. Messenger RNA (mRNA) levels of BECN1 (Fig. 5b, g) and ATG4C (Fig. 5c, h) were decreased both in SKBR3 (Fig. 5b, c) and MDA (Fig. 5g, h) cells that were treated with MIR376B-loaded SP-AH particles (SP-AH/MIR376B) compared to controls, but not with unloaded-SP-AH nanoparticles (Additional file 1: Fig. S6a, b).Furthermore, a decrease in target protein levels were observed in SKBR3 (Fig. 5d, e) and MDA cells (Fig. 5i, j) that were treated with SP-AH/MIR376B particles but not with SP-AH alone.
Next, autophagic activity in cells were determined using MAP1LC3B (shortly LC3) as an autophagy marker. In fact, autophagy-related lipidation of free LC3-I form of the protein leads to the formation of autophagosome-incorporated LC3-II form, resulting in a punctuate cytosolic staining pattern. Lipidation also changes migration of the protein in SDS-PAGE protein gels (18 kDa LC3-I versus 16 kDa LC3-II). LC3 dot counts and LC3-II/I ratio analysis are commonly used as autophagy detection tests. SKBR3 or MDA cells were treated with SP-AH nanoparticles with or without MIR376B loading, followed by autophagy assessment. SP-AH/MIR376B significantly inhibited LC3 dot-formation and decreased LC3-II/I ratios in SKBR3 (Fig. 5k–m) and MDA (Fig. 5n–p) cells compared to miRNA-free SP-AH nanoparticles. Hence, we conclude that, AGO2 protein containing and MIR376B-loaded SP-AH particles are able to efficiently downregulate autophagy-related targets of the miRNA and inhibit autophagic activity in breast cancer cells.
SP-AH-mediated delivery of MIR376B and suppression of autophagy in a xenograft tumor model of breast cancer
In order to explore nucleic acid delivery potential of SP-AH nanoparticles in vivo in mice, we created a xenograft tumor model of human breast cancer. For that purpose, MDA cells were subcutaneously injected to nude mice and when tumors reached 50 mm3 in about 30 days, MIR376B-loaded SP-AH nanoparticles were administered i.v. through the tail vein. Six days later, tumor samples were collected and analyzed. First, miRNA delivery to tumors was confirmed by qPCR.
As shown in Fig. 6a, MIR376B levels were increased by several folds in tumor samples that were collected from nanoparticle-injected mice compared to PBS-injected controls. MiRNAs that were delivered by nanoparticles were highly functional since MIR376B targets BECN1 (Fig. 6b) and ATG4C (Fig. 6c) were significantly suppressed in tumor tissues. The effect of the miRNA on target protein levels were also tested and autophagy levels were evaluated using LC3 as a marker. Immunostaining of tissue sections using specific antibodies showed a clear reduction in BECN1 and ATG4C levels (Fig. 6d) in tumor samples from SP-AH/MIR376B-injected mice. LC3 antibodies with a higher affinity to LC3-II were used to assess the autophagic activity of tumors. Although a strong LC3-II signal was observed in control samples, tumors from SP-AH/MIR376B-injected mice had a clearly lower signal (Fig. 6d). MiRNA-mediated decrease in BECN1 and ATG4C protein levels were confirmed in immunoblots of tumor protein extracts (Fig. 6e). Moreover, immunoblotting with an LC3 antibody that recognized both LC3-I and LC3-II with similar affinities showed that LC3-II/I ratios were decreased in tumors from SP-AH/MIR376B-injected mice, confirming autophagy inhibition in these tumors (Fig. 6e). All these results showed that miRNA mimics were delivered in vivo into tumors by SP-AH nanoparticles in a targeted manner. Resulting increase in intratumoral miRNA levels was sufficient for the downregulation of miRNA target mRNAs and proteins, and for the suppression of autophagy.
Combination of MIR376B-loaded SP-AH nanoparticles with cisplatin in breast cancer treatment
Increased autophagic activity in tumors was associated with metabolic adaptation and survival of cancer cells as well as their resistance to chemotherapy . Consequently, combination of chemotherapeutic agents with autophagy inhibitors was tested in a number of preclinical and clinical studies [38,39,40]. Having established that SP-AH-mediated delivery of MIR376B strongly inhibited autophagy in xenografted human breast cancer tumors, we checked whether combination of miRNA-loaded functional nanoparticles would increase the efficacy of chemotherapy.
First, SKBR3 or MDA cells were treated with cisplatin alone or in combination with SP-AH or SP-AH/MIR376B nanoparticles. While combination with SP-AH particles did not affect cisplatin toxicity in breast cancer cells, SP-AH/MIR376B co-treatment significantly increased anti-cancer activity of cisplatin (Fig. 7a).
Next, effects of nanoparticle-mediated autophagy inhibition on chemotherapy were tested in vivo in the xenograft mice model. Following establishment of tumors (30 days after subcutaneous injection and tumor size of 50 mm3), nude mice were injected with PBS, cisplatin alone or in combination with SP-AH/MIR376B nanoparticles. In order to clearly reveal the contribution of miRNA-loaded nanoparticles to the chemotherapeutic effect of the drug, a time point and a dose (4 days after 6 mg/kg cisplatin injection) resulting in a mild anti-tumor effect, was chosen (Fig. 7b). Under these conditions, combination of SP-AH/MIR376B nanoparticles with cisplatin resulted in a significant reduction in tumor volume and gave rise to superior anti-tumor effects compared to single treatment (Fig. 7c–e).
One major roadblock in gene therapy is the lack of safe delivery vehicles. Nanoparticles are promising gene delivery tools, yet commonly used cationic particles are generally toxic. Based on the observation that AGO2 proteins stabilized free microRNAs in blood circulation, here we proposed the usage of AGO2 proteins as non-cationic, non-toxic and effective nucleic acid delivery agents. We demonstrated that nanoparticles functionalized by AGO2 conjugation and autophagy inhibitory miRNA addition may be used as potent adjuvant treatment tools increasing the efficacy of classical chemotherapy.
Addition of AGO2 protein as well as anti-HER2 antibody onto a PAA-coated SPION core, resulted in the creation of novel theranostic nanoparticles (SP-AH). We showed that: (i) SP-AH nanoparticles specifically and selectively targeted HER2-positive breast cancer cells and their xenograft tumors; (ii) they were efficiently internalized by cancer cells; (iii) they delivered autophagy inhibitory miRNA, MIR376B, into cancer cells and tumor tissues; (iv) targeted delivery of MIR376B successfully downregulated autophagy-related targets of the miRNA, resulting in a strong inhibition of autophagy in cells and tumors; (v) combination of MIR376B-loaded SP-AH nanoparticles with a classical chemotherapy drug revealed the potential of these innovative nanoparticles as adjuvant cancer treatment agents. SP-AH nanoparticles were highly biocompatible since cellular toxicity tests, blood biochemistry and complete blood count analyses, detailed histopathological examination of major organs and tissues showed no detectable short- or long-term (40 days) side-effects. All these results indicate that nucleic acid-carrier SP-AH nanoparticles have the potential to be safely used as chemotherapy enhancing novel adjuvant agents.
Mammalian AGO proteins are able to attach to various types of small RNAs with similar binding affinities . Therefore, SP-AH nanoparticles may be used as general small RNA and even nucleic acid delivery agents in experimental and pre-clinical studies. Future tests, including clinical studies, will prove the potential of these particles as novel adjuvant cancer treatment agents.
Materials and methods
Double stranded MIR376B mimics were purchased from Dharmacon (C-300741-03-0005). FLAG-Ago2 was a gift from Edward Chan (Addgene plasmid #21538). PECFP-Rab5 and pECFP-Rab9 plasmids were kind gifts from Batu Erman. FeCl3·6H20 and FeCl2·4H2O were purchased from Merck (U.S.A). Ammonium hydroxide (26%), poly(acrylic acid sodium salt) (Mw 2100 g/mol), Bradford reagent, bovine serum albumin (BSA) and potassium phosphate dibasic anhydrous were purchased from Aldrich (U.S.A.). Phosphate buffer saline (PBS) and 2-(N-morpholino) ethane sulfonic acid (MES monohydrate) buffers were purchased from Biomatik (Canada). Ethylenediaminetetraacetic acid (EDTA) disodium salt was purchased from Multicell (U.S.A.). Potassium phosphate monobasic was purchased from Riedel-de Haën (U.S.A.). N–N dimethylformamide (DMF) was purchased from Merck-Milipore (U.S.A.) ethyl-3-(3-dimethylaminopropyl) carbodiimide (EDC), N-hydroxysulfosuccinimide (sulfo-NHS), DyLight 650 NHS ester, Ellman’s Reagent, Traut’s Reagent and Slide-A-Lyzer 10 k and 20 k dialysis cassettes were purchased from Thermo Scientific (U.S.A.). antiHer2 was purchased from eBioscience (U.S.A.). Human AGO2 (His-tag) (EIF2C2) recombinant protein was purchased from Sino Biological Inc. (China). Maleimide-polyethyleneglycol-amine (Mal-PEG-NH2) (2 kDa) was purchased from Nanocs (U.S.A.). Vivaspin 20 (MWCO 30,000) polyethylenesulfonate (PES) filters were purchased from Sartorius (Germany). Float-A-Lyzer (MWCO 150,000) was purchased from Spectrumlabs (U.S.A).
Photoluminescence spectra and absorbance spectra were (PL) recorded on a Horiba Jobin–Yvon FluoroMax-3 and UV-3600 Shimadzu UV–VIS-NIR spectrophotometer, respectively, at room temperature. Hydrodynamic size was measured by Dynamic light scattering (DLS) using Zetasizer Nano Series ZS at room temperature with 173° backscattered angle. Functional groups analysis was performed using the dried samples and Thermo Scientific Nicolet iS10 ATR-IR. Transmission electron microscopy (TEM) images were taken by Techani G2 F30 at brightfield high resolution (HR) TEM (acceleration voltage 200 kV). STEM images were taken at Hitachi HD2700 Dedicated STEM with Cs corrector (acceleration voltage 200 kV) and EDX analysis were performed with Oxford X-MaxN 100 TLE 100 mm2 Dual detector assignment system. Samples were deposited on carbon coated Cu-grid from dilute solutions. Vibrating Sample Magnetometry (VSM) measurements were conducted with Cryogenic limited PPMS at ambient conditions using the dried powder samples. TA Q500 (Thermogravimetric analysis (TGA)) was used to determine the organic content of SP nanoparticles under nitrogen atmosphere at a hearing rate of 10 °C/min. Tissues of nude mice models were homogenized by homogenizer, light duty, Isolab. Perkin Elmer IVIS® Lumina III In Vivo Imaging System was used for optical imaging (Ex: 650, Em: 670).
Synthesis of poly(acrylic acid) coated SPIONs (SP)
Poly(acrylic acid) (PAA) coated SPIONs were synthesized according to published aqueous precipitation method  using FeCl3·6H2O, FeCl2·4H2O, ammonium hydroxide under nitrogen. [PAA]:[Fe2+]:[Fe3+]:[OH−] mole ratio of 3:2:1:6 was used in the synthesis and particle growth was allowed for 1 h at 85 °C. Reaction mixture was cooled down to room temperature, placed on a 0.3 Tesla magnetic field overnight, then the precipitates were removed (if any), and colloidal suspension was washed with DI water using ultracentrifuge tubes (10 kDa MWCO PES filter). For the analysis requiring solid particles, part of the washed colloidal solution was lyophilized. The rest was stored at room temperature.
Synthesis of AGO2 conjugated SPIONs (SP-A)
50 mg of SP was activated by mixing with 14 mg of EDC and 14.4 mg of sulfo-NHS in MES buffer at pH 6.0 and room temperature for 15 min. Then, NHS active SPIONs were washed with PBS (pH 7.4) via ultracentrifugation (10 kDa MWCO Amicon filter) at room temperature. AGO2 protein (150 µg) was added to sulfo-NHS activated nanoparticles and mixed 48 h at + 4 °C. Reaction was quenched with excess hydroxylamine and SP-A was purified with MES buffer (pH 6.0) via dialysis (150 kDa Float-A-Lyzer) for 12 h at + 4 °C with 4 times buffer refreshment.
Activation of SP-A with maleimide groups (SP-A/MI)
SP-A was activated with EDC/sulfo-NHS and purified using the method given for SP synthesis. It was reacted with 3 mg NH2-PEG-Mal (2000 Da) for 48 h at + 4 °C and quenched with excess hydroxylamine. Product was purified using ultracentrifugation (10 kDa MWCO amicon filter) at + 4 °C.
Fluorescent tagging of anti-HER2 (anti-HER2-dye)
Commercially available NHS active dye (Dylight 650®) was dissolved in DMF (10 mg/ml). anti-HER2 antibody was dissolved in sodium borate buffer at pH 8.55. Antibody and dye solutions were mixed in the molar ratio of [antiHer2]:[Dye] = 1:10 at room temperature for 1 h. Dye conjugated anti-HER2 was purified with dialysis using 20 kDa MWCO dialysis cassette (Slide-A-Lyzer) against phosphate/EDTA buffer (pH: 8.5) at + 4 °C with 4 times buffer refreshment in 12 h. Protein concentration and molar ratio of protein and dye was calculated using the following formula:
Thiolation of anti-HER2 (anti-HER2-Dye-SH)
Anti-HER2-Dye was mixed with Traut’s Reagent at pH 8 with the molar ratio of [1:100] at room temperature for 2 h, then purified with dialysis from 10 k MWCO dialysis cassette at + 4 °C with 6 times buffer refreshment in PBS/EDTA in 4 h. Sulfhydryl groups on antiHer2 was quantified using Ellman’s reagent. For this, 25 µl Ellman’s reagent (1 mg/ml) was mixed with 25 µl of anti-HER2-dye-SH at room temperature for 15 min, then absorbance at 412 nm was measured to calculate the concentration of thiol units using the Beer Lambert equation as follows:
Synthesis of anti-HER2-Dye conjugated SPIONs (SPION/AGO2/anti-HER2-dye)
Freshly prepared anti-HER2-dye-SH was mixed with maleimide functionalized nanoparticles (SP-A/MI) in PBS/EDTA at pH 7.2 for 1 h at room temperature and then overnight at + 4 °C. The product was purified with the dialysis from 300 kDa MWCO dialysis membrane at + 4 °C with 4 times buffer refreshment in PBS.
Determination of AGO2 concentration on SPIONs by Bradford Assay
Bovine serum albumin (BSA) protein at 0, 1, 2, 4, 6, 8, 10 µg/ml in PBS was prepared as the reference. Dialysis product (dialysate) of SP-A was concentrated and measured as the analyte. 1 ml of each reference and analyte samples were mixed with 1 ml of Bradford Reagent for 10 min at room temperature, then absorbance at 595 nm was recorded using UV–vis spectroscopy. Data from the BSA was used to create the calibration curve (Adj. R2 = 0.9950). Since SPIONs have some absorbance at that wavelength, the amount of AGO2 was confirmed directly by the analysis of SP-A (66 µg/ml; 5.5 µg AGO2 per mg of nanoparticles) and indirectly by the analysis of unbounded AGO2 protein recovered from the dialysate. Unbounded amount of AGO2 was calculated as 11.6 µg/ml which agrees with the bounded amount.
Determination of anti-HER2 concentration on SPIONs by photoluminescence detection
Amount of DyLight 650® conjugated to anti-Her2 and SPIONs was calculated from the luminescence intensity of the dye at 672 nm. Briefly, first a calibration curve for DyLight 650® was created from the dye dissolved in PBS in 2 × 10−2, 1 × 10−2, 4 × 10−3, 2 × 10−3, 1 × 10−3, 5 × 10−4 µM concentrations and their emission intensity at 672 nm was recorded on Fluoromax-3. Linear fit provided the following equation to be used in the sample analysis: PL intensity = 3.01 × 108 DyLight 650® conc. + 1.2 × 105, R2 = 0.998. Emission intensity of SP–AH was measured as 1.8 M (a.u) at 672 nm (dilution factor = 20) and placed into the equation to find concentration of dye on SPIONs (0.114 nmol). To calculate the concentration of antiHer2 on SPIONs, the molar ratio between anti-HER2 and dye was used (anti-HER2:Dye = 1:0.8). According to this calculation, the mole number of antiHer2 was found as 0.142 nmol. Using the molecular weight of anti-HER2 (148,000 g/mol) concentration of anti-HER2 in SPION solution was calculated as 19 µg/ml.
This information, molecular weight of anti-HER2 (148,000 g/mol) and the mole ratio of antiHer2:Dye (1:08) indicates that dye labeled SP-AH nanoparticles contain 0.142 nmol or 19 µg/ml anti-HER2.
Quantification of number of AGO2 and anti-HER2 per nanoparticle
Number of proteins per nanoparticle was calculated using the following equation:
where a is the mole number of proteins in 1 cm3, N is Avogadro’s number, V is the volume of nanoparticles in 1 cm3 and r is the mean radius of nanoparticles (z-average hydrodynamic size). V is calculated by subtracting volume of water in 1 cm3 nanoparticle suspension. Volume of water in 1 cm3 dispersion was also found over mass of water in 1 cm3 dispersion: Masswater = Massliquid NPs − Masssolid NPs.
Analysis of iron content in the mice tissues by inductively coupled plasma mass spectroscopy (ICP-MS) method
In order to digest the tissues and etch the iron oxide nanoparticles, the weighed organs were homogenized in the concentrated 500 μls of H2SO4, HNO3 and H2O2 and aged for a week. After complete digestion of the tissues, the resulting solutions were diluted to 20 ml with distilled water and the contents were detected by ICP-MS using iron standard curve as a reference, then the amount of iron per mg of organ was calculated.
Cell culture and transfection
HEK293T human embryonic kidney cells and the breast cancer cell lines MCF7 and MDA-MB-453 were cultured in Dulbecco’s modified Eagle’s medium (DMEM, Biological Industries, #BI01-050-1A), and the other breast cancer cell line SKBR3 was cultured in McCoy’s 5A medium (PAN, #P04-05500). Both of the culture media were supplemented with 10% (v/v) fetal bovine serum (FBS, PAN, #P30-3302), antibiotics (Penicillin/streptomycin, Biological Industries, #BI03-031-1B) and l-glutamine (Biological Industries, #BI03-020-1B) in a 5% CO2 humidified incubator at 37 °C. HEK293T cells were transiently transfected with calcium phosphate transfection method according to standard protocols. SKBR3 cells were transfected with polyethyleneimine (PEI) method according to standard protocol.
MiRNA loading to nanoparticles
MIR376B microRNAs were loaded to nanoparticles by incubating nanoparticles in an RNA binding buffer (100 mM KCl, 2 mM MgCl2, 10 mM Tris–HCl in DEPC water) together with 20 nM MIR376B mimics at 4 °C for 2 h by rotating. 150 µg/ml of each nanoparticle or equal volume of PBS with nanoparticles were incubated in the same way and cells were treated with these nanoparticles or PBS for 48 h.
Immunoblotting and antibodies
Cells were lysed at indicated time points in RIPA buffer (50 mM TRIS–HCl pH 7.4, 150 mM NaCl, 1% NP40, 0.25% Na-deoxycholate) supplemented with a complete protease inhibitor cocktail (Roche, 04-693-131-001) and 1 mM phenylmethylsulfonyl fluoride (PMSF, Sigma-Aldrich, P7626). Protein extracts (30 µg per well) were separated using 10–15% SDS-polyacrylamide gels (SDS-PAGE), and then transferred onto nitrocellulose membranes (Millipore, #IPVH00010). Membranes were blocked in 5% nonfat milk (Applichem, #A0830) in PBST (3.2 mM Na2HPO4, 0.5 mM KH2PO4, 1.3 mM KCl, 135 mM NaCl, and 0.05% Tween 20, pH 7.4) for 1 h and then incubated with primary antibodies in a 3% BSA PBST solution: anti-AGO2 (Cell Signaling Technology, #2897), anti-Flag (Sigma, A494842), anti-BECN1 (Santa Cruz, sc-11427), anti-ATG4C (Sigma-Aldrich, AB75056), anti-LC3 (CST #2775) and anti-β-ACTIN (Sigma-Aldrich, A5441) antibody as loading control. Following PBST washes, membranes were incubated with horseradish peroxidase (HRP)-coupled secondary anti-mouse (Jackson Immunoresearch laboratories, #115035003) or anti-rabbit antibodies (Jackson Immunoresearch Laboratories, #111035144). Band intensities were quantified using the ImageJ software . For dot blot assays, 96-well Bio-Dot module (BioRad, #1706547) was used. 50 µg of protein extracts were transferred onto nitrocellulose membrane under vacuum according to the manufacturer’s instructions. Then, the membrane was blocked, washed and treated with primary and secondary antibodies as described above. Full blot images of representative experiments supported in Additional file 1: Fig. S8.
Cells were cultured on cover slides and treated with 150 µg of nanoparticles for indicated time periods, then fixed in ice-cold 4% paraformaldehyde/PBS. For colocalization experiments, cells were transfected in advance with GFP-Rab5orGFP-Rab9 plasmids and treated with nanoparticles after 48 h. Cells were fixed in ice-cold 4% paraformaldehyde/PBS. Following the fixation, nuclei were stained using Hoechst (Invitrogen, 31716 W) in PBS. Coverslides were mounted onto glass slides, and samples were analyzed with a Carl Zeiss LSM 710 confocal microscope (Zeiss, Germany). For indirect immunostaining experiments, following fixation, cells were permeabilized in PBS containing 0.1% BSA (Sigma, #A4503) and 0.1% saponin (Sigma, #84510). As primary antibodies, anti-LC3 (Sigma, L8918), anti-BECN1 (Santa Cruz, sc-11427) and anti-ATG4C (Sigma-Aldrich, AB75056) were used. Anti-mouse Alexa Fluor 488 (Invitrogen, #A32723) and anti-rabbit (Invitrogen, #A-11008) were used as secondary antibodies. Coverslides were mounted onto glass slides, and samples were analyzed using a BX60 fluorescence microscope (Olympus, BX60) or Carl Zeiss LSM 710 confocal microscope (Zeiss, Germany).
HEK293T cells were cultured and transfected with flag-AGO2 for 72 h. 25 µg of anti-Flag M2 Affinity Gel beads were put into an eppendorf tube and prewashed with 1 ml cold PBS, 3 times with RIPA and 2 times with RIPA++ (supplemented with protease inhibitors cocktail and 1 mM PMSF) for 1 min at 6000 rpm, at + 4 °C. 2000 µg of protein solution was loaded on beads (Sigma, # A2220), rotated overnight at + 4 °C. After o/n incubation, beads were washed with RIPA++ and centrifuged at 6000 rpm, at + 4 °C, 1 min for 5 times. Then beads were treated with loading dye for IP control with anti-flag antibody and TRIzol reagent for RNA isolation. For long-term miRNA stability test, immunoprecipitated beads were incubated at room temperature for 21 days, and then RNA isolation was done with TRIzol reagent.
RNA isolation and RT-PCR analyses
Total RNA was extracted using TRIzol reagent (Sigma-Aldrich, #T9424) according to the manufacturer’s instructions. cDNA was reverse transcribed from DNase-treated total RNA using M-MuLV reverse transcriptase (Fermentas, #EP0351), random hexamers (Invitrogen, #48190-011) and MIR376B stem-loop primer. For single-step qRT-PCR reaction, SYBR Green Quantitative RT-PCR kit (Roche, #04-913-914-001) and a LightCycler 480 (Roche) were used. To activate the SYBR green, an initial cycle of 95 °C, for 10 min was performed followed by PCR reactions: 40 cycles of 95 °C for 15 s and 60 °C for 1 min. Then a thermal denaturation protocol was used to generate the dissociation curves for the verification of amplification specificity (a single cycle of 95 °C for 60 s, 55 °C for 60 s and 80 cycles of 55 °C for 10 s). Changes in mRNA levels were quantified with the 2−ΔΔCT method and normalized to GAPDH (glyceraldehyde-3-phosphate dehydrogenase) mRNA. Primers used during the study were: BECN1 primers 5′-AGGTTGAGAAAGGCGAGACA-3′; 5′-GCTTTTGTCCACTGCTCCTC-3′; ATG4C primers 5′-GCATAAAGGATTTCCCTCTTGA-3′; 5′-GCTGGGATCCATTTTTCG-3′, and GAPDH primers 5′-AGCCACATCGCTCAGACAC-3′; 5′-GCCCAATACGACCAAATCC-3′. TaqMan qRT-PCR reactions were performed using FastStart Universal Probe Master kit (ROCHE, #04913957001) and LightCycler 480 (Roche) according to the protocols described previously . Primers and the probe used during the study were: MIR376B, Stem-loop primer, 5′-GTCGTATCCAGTGCAGGGTCCGAGGTATTCGCACTGGATACGACAACATGG-3′; Forward primer, 5′-GTTAATCATAGAGGAAAAT-3′; Reverse primer, 5′-GTGCAGGGTCCGAGGT-3′; TaqMan Probe, 5′(6-FAM)- GCA GGG GCC ATG CTA ATC TTC TCT GTA TCG -(TAMRA-sp)3′; U6, Forward primer, 5′-CTCGCTTCGGCAGCACA-3′; Reverse primer, 5′-RAACGCTTCACGAATTTGCGT-3′; TaqMan Probe 5′(6-FAM)-GCA GGG GCC ATG CTA ATC TTC TCT GTA TCG-(TAMRA-Sp)3′.
Flow cytometry analysis
Nanoparticles were labelled with Alexa-flour-647 dye in order to monitor the targeting specificity of anti-Her2 tagged nanoparticles for HER2 receptor overexpressing cells via flow cytometry. MCF7, MDA-MB-453 and SKBR3 cells were seeded onto 12-well plate and treated with the nanoparticles for indicated times. At the end of incubation, cells were washed 2 times with PBS and trypsinized. Cells were fixed by using ice-cold 70% ethanol and then resuspended in PBS. The Alexa-flour-647 positive cells were detected using BD FACS Canto™ instrument and analyzed using Flow Jo software (Tree Star Inc). A minimum of 10,000 events per sample corresponding to gated population were collected, and cellular debris was not counted. Nanoparticles without an anti-HER2 antibody on their surface in which Alexa-flour-647 dye were conjugated on SPION/PAA (SP-F) and SPION/PAA/AGO2 (SP-AF) nanoparticles, were served for understanding of anti-HER2 antibody-derived targeting.
A 3-(4,5-dimethylthiazol-2-yl)-2,5-diphenyl tetrazolium bromide (MTT) assay was performed to evaluate the influence of the cisplatin, nanoparticle and the combination on cell viability. MDA-MB-453 and SKBR3 cells were seeded onto 96-well plates and cultured with the same conditions above. After 24 h, cells were treated with cisplatin or nanoparticle complexes for 48 h. Prior to the MTT reagent administration we washed the media and 10 µl of 5 mg/ml MTT reagent was added into 100 µl of cell medium and incubated for 4 h in a 5% CO2 humidified incubator at 37 °C. At the end of 4 h, the medium was removed, and formazan crystals were solubilized with dimethyl sulfoxide (DMSO) for 10 min at room temperature. The absorbance at 570 nm was determined with a reference filter at 650 nm for each well using a Microplate absorbance reader (Biorad, iMark). Cell viability of each group was expressed as a percentage of viability of untreated control cells.
In vivo studies
All animal experiments were approved by the Ethics Committee of the Koç University in accordance with the guidelines on animal care and use (File No: 2013-3). NPs were passed through 0.2 micron sterile filter before administered to animals. For cytotoxicity assays, nude mice (6–8 weeks) were intravenously (i.v.) injected with (10 mg Fe per kg of mice) nanoparticles and inoculated for indicated time periods (10 or 40 days). At the end of inoculation, blood samples were collected by intracardiac puncture under anesthesia, and serum biochemical parameters [ALB (albumin), ALKP ((alkaline phosphatase), ALT (alanine aminotransferase), AMYL (amylase), Ca (calcium), GLU (glucose), LIPA (lipase), TBIL (total bilirubin), TP (total protein), BUN (blood urea nitrogen) and GLOB (globulin)] were analyzed by using diagnostic health profile kit (IDEXX VetTestTM, #6802590) on an Olympus AU400 according to manufacturer’s instructions. Complete blood count test was performed with the same mice on machine (PROKAN, #PE-6800).
Formalin-fixed mice tissues embedded in paraffin, cut at 4-micron using a microtome. After transfer on slides and air-drying and they were baked for 15 min at 60 °C. Deparaffinization and rehydration were achieved by immersing slides in xylene, 100% ethanol, and 70% ethanol. Following the boiling in 10 mM sodium citrate buffer (pH 6.0), and cooling, slides were counterstained with hematoxylin and eosin.
A xenograft mouse model was generated by subcutaneous injection of SKBR3 and MDA-MB-453 cells [1 × 107 cells per mouse embedded in Matrigel (BD Biosciences, #356234)] in the right front flank of female nude mice (6–8 weeks, ~ 24 g). When the tumors reached ~ 50–100 mm3, approximately 4 weeks after inoculation, the tumor bearing mice were injected via tail vein a single dose of nanoparticles (10 mg/kg Fe+2). At the indicated time points, in vivo imaging of the nanoparticles was conducted under isoflurane inhalation anesthesia by using IVIS Spectrum imaging system (Caliper Life Sciences) with the Living Image software package. Anesthetized mice were euthanized through cervical dislocation and dissected to remove tumors, livers, brain, intestine, stomach, uterus, kidneys, spleens, hearts, and lungs which were placed into 10% Formalin for pathology investigation.
For microRNA delivery experiments, MIR376B microRNAs were bound to SP-AH nanoparticles as explained above and i.v. injected to mice bearing MDA-MB-453 tumor. After 6 days of injection, mice were euthanized, and RNA and protein levels were investigated. For cisplatin-combination analysis, tumors were generated, and nanoparticle were injected as the above. Then, 2 days after the nanoparticle injection, 6 mg/kg cisplatin were intraperitoneally (i.p.) injected. 6 mg/kg dose is equivalent to the human equivalent dose used in the clinic  and in line with previous animal studies [50, 51]. Four days after cisplatin injection, relative changes in tumor volume were determined by caliper measurements and compared to measurements in PBS injected control mice.
Statistical analyses were performed using Student’s two-tailed t test. Data were represented as means of ± SD of independent experiments (biological replicates). Values of p < 0.05 were considered as being significant (*p < 0.05, **p < 0.03, ***p < 0.01). Reactions were performed in duplicates and number of independent experiments (n) was marked.
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Katz MG, Fargnoli AS, Williams RD, Bridges CR. Gene therapy delivery systems for enhancing viral and nonviral vectors for cardiac diseases: current concepts and future applications. Hum Gene Ther. 2013;24:914–27.
Nayerossadat N, Maedeh T, Ali PA. Viral and nonviral delivery systems for gene delivery. Adv Biomed Res. 2012;1:27.
Thomas CE, Ehrhardt A, Kay MA. Progress and problems with the use of viral vectors for gene therapy. Nat Rev Genet. 2003;4:346–58.
Babaei M, Eshghi H, Abnous K, Rahimizadeh M, Ramezani M. Promising gene delivery system based on polyethylenimine-modified silica nanoparticles. Cancer Gene Ther. 2017;24:156–64.
Kokil GR, Veedu RN, Le BT, Ramm GA, Parekh HS. Self-assembling asymmetric peptide-dendrimer micelles—a platform for effective and versatile in vitro nucleic acid delivery. Sci Rep. 2018;8:4832.
Cosco D, Cilurzo F, Maiuolo J, Federico C, Di Martino MT, Cristiano MC, Tassone P, Fresta M, Paolino D. Delivery of miR-34a by chitosan/PLGA nanoplexes for the anticancer treatment of multiple myeloma. Sci Rep. 2015;5:17579.
Guan S, Rosenecker J. Nanotechnologies in delivery of mRNA therapeutics using nonviral vector-based delivery systems. Gene Ther. 2017;24:133–43.
Nitta SK, Numata K. Biopolymer-based nanoparticles for drug/gene delivery and tissue engineering. Int J Mol Sci. 2013;14:1629–54.
Hom C, Lu J, Tamanoi F. Silica nanoparticles as a delivery system for nucleic acid-based reagents. J Mater Chem. 2009;19:6308–16.
Ding Y, Jiang Z, Saha K, Kim CS, Kim ST, Landis RF, Rotello VM. Gold nanoparticles for nucleic acid delivery. Mol Ther. 2014;22:1075–83.
Jarockyte G, Daugelaite E, Stasys M, Statkute U, Poderys V, Tseng TC, Hsu SH, Karabanovas V, Rotomskis R. Accumulation and toxicity of superparamagnetic iron oxide nanoparticles in cells and experimental animals. Int J Mol Sci. 2016;17:1193.
Mok H, Zhang M. Superparamagnetic iron oxide nanoparticle-based delivery systems for biotherapeutics. Expert Opin Drug Deliv. 2013;10:73–87.
Gozuacik D, Yagci-Acar HF, Akkoc Y, Kosar A, Dogan-Ekici AI, Ekici S. Anticancer use of nanoparticles as nucleic acid carriers. J Biomed Nanotechnol. 2014;10:1751–83.
Kim YK, Zhang M, Lu JJ, Xu F, Chen BA, Xing L, Jiang HL. PK11195-chitosan-graft-polyethylenimine-modified SPION as a mitochondria-targeting gene carrier. J Drug Target. 2016;24:457–67.
Mykhaylyk O, Zelphati O, Rosenecker J, Plank C. siRNA delivery by magnetofection. Curr Opin Mol Ther. 2008;10:493–505.
Oral O, Cikim T, Zuvin M, Unal O, Yagci-Acar H, Gozuacik D, Kosar A. Effect of varying magnetic fields on targeted gene delivery of nucleic acid-based molecules. Ann Biomed Eng. 2015;43:2816–26.
Pan Z, Shi Z, Wei H, Sun F, Song J, Huang Y, Liu T, Mao Y. Magnetofection based on superparamagnetic iron oxide nanoparticles weakens glioma stem cell proliferation and invasion by mediating high expression of microRNA-374a. J Cancer. 2016;7:1487–96.
Chiou GY, Cherng JY, Hsu HS, Wang ML, Tsai CM, Lu KH, Chien Y, Hung SC, Chen YW, Wong CI, et al. Cationic polyurethanes-short branch PEI-mediated delivery of Mir145 inhibited epithelial-mesenchymal transdifferentiation and cancer stem-like properties and in lung adenocarcinoma. J Control Release. 2012;159:240–50.
Strand SP, Lelu S, Reitan NK, de Lange Davies C, Artursson P, Varum KM. Molecular design of chitosan gene delivery systems with an optimized balance between polyplex stability and polyplex unpacking. Biomaterials. 2010;31:975–87.
Luo D, Haverstick K, Belcheva N, Han E, Saltzman WM. Poly(ethylene glycol)-conjugated PAMAM dendrimer for biocompatible, high-efficiency DNA delivery. Macromolecules. 2002;35:3456–62.
Reineke TM, Davis ME. Structural effects of carbohydrate-containing polycations on gene delivery. 1. Carbohydrate size and its distance from charge centers. Bioconjug Chem. 2003;14:247–54.
Lv H, Zhang S, Wang B, Cui S, Yan J. Toxicity of cationic lipids and cationic polymers in gene delivery. J Control Release. 2006;114:100–9.
Ha M, Kim VN. Regulation of microRNA biogenesis. Nat Rev Mol Cell Biol. 2014;15:509–24.
Ullah S, John P, Bhatti A. MicroRNAs with a role in gene regulation and in human diseases. Mol Biol Rep. 2014;41:225–32.
Gozuacik D, Akkoc Y, Ozturk DG, Kocak M. Autophagy-regulating microRNAs and cancer. Front Oncol. 2017;7:65.
Wang HW, Noland C, Siridechadilok B, Taylor DW, Ma E, Felderer K, Doudna JA, Nogales E. Structural insights into RNA processing by the human RISC-loading complex. Nat Struct Mol Biol. 2009;16:1148–53.
Glinge C, Clauss S, Boddum K, Jabbari R, Jabbari J, Risgaard B, Tomsits P, Hildebrand B, Kaab S, Wakili R, et al. Stability of circulating blood-based MicroRNAs—pre-analytic methodological considerations. PLoS ONE. 2017;12:e0167969.
Arroyo JD, Chevillet JR, Kroh EM, Ruf IK, Pritchard CC, Gibson DF, Mitchell PS, Bennett CF, Pogosova-Agadjanyan EL, Stirewalt DL, et al. Argonaute2 complexes carry a population of circulating microRNAs independent of vesicles in human plasma. Proc Natl Acad Sci USA. 2011;108:5003–8.
Schwarzenbach H, Nishida N, Calin GA, Pantel K. Clinical relevance of circulating cell-free microRNAs in cancer. Nat Rev Clin Oncol. 2014;11:145–56.
Turchinovich A, Burwinkel B. Distinct AGO1 and AGO2 associated miRNA profiles in human cells and blood plasma. RNA Biol. 2012;9:1066–75.
Turchinovich A, Weiz L, Langheinz A, Burwinkel B. Characterization of extracellular circulating microRNA. Nucleic Acids Res. 2011;39:7223–33.
MacRae IJ, Ma E, Zhou M, Robinson CV, Doudna JA. In vitro reconstitution of the human RISC-loading complex. Proc Natl Acad Sci USA. 2008;105:512–7.
Rivas FV, Tolia NH, Song JJ, Aragon JP, Liu J, Hannon GJ, Joshua-Tor L. Purified Argonaute2 and an siRNA form recombinant human RISC. Nat Struct Mol Biol. 2005;12:340–9.
Lima WF, Wu H, Nichols JG, Sun H, Murray HM, Crooke ST. Binding and cleavage specificities of human Argonaute2. J Biol Chem. 2009;284:26017–28.
Tan GS, Garchow BG, Liu X, Yeung J, Morris JPt, Cuellar TL, McManus MT, Kiriakidou M. Expanded RNA-binding activities of mammalian Argonaute 2. Nucleic Acids Res. 2009;37:7533–45.
Korkmaz G, le Sage C, Tekirdag KA, Agami R, Gozuacik D. miR-376b controls starvation and mTOR inhibition-related autophagy by targeting ATG4C and BECN1. Autophagy. 2012;8:165–76.
Oral O, Akkoc Y, Bayraktar O, Gozuacik D. Physiological and pathological significance of the molecular cross-talk between autophagy and apoptosis. Histol Histopathol. 2016;31:479–98.
Levy JM, Thorburn A. Targeting autophagy during cancer therapy to improve clinical outcomes. Pharmacol Ther. 2011;131:130–41.
White E. The role for autophagy in cancer. J Clin Invest. 2015;125:42–6.
Levy JMM, Towers CG, Thorburn A. Targeting autophagy in cancer. Nat Rev Cancer. 2017;17:528–42.
Owens MA, Horten BC, Da Silva MM. HER2 amplification ratios by fluorescence in situ hybridization and correlation with immunohistochemistry in a cohort of 6556 breast cancer tissues. Clin Breast Cancer. 2004;5:63–9.
Qu X, Sheng J, Shen L, Su J, Xu Y, Xie Q, Wu Y, Zhang X, Sun L. Autophagy inhibitor chloroquine increases sensitivity to cisplatin in QBC939 cholangiocarcinoma cells by mitochondrial ROS. PLoS ONE. 2017;12:e0173712.
Zhao XG, Sun RJ, Yang XY, Liu DY, Lei DP, Jin T, Pan XL. Chloroquine-enhanced efficacy of cisplatin in the treatment of hypopharyngeal carcinoma in xenograft mice. PLoS ONE. 2015;10:e0126147.
Ma L, Xu Y, Su J, Yu H, Kang J, Li H, Li X, Xie Q, Yu C, Sun L, Li Y. Autophagic flux promotes cisplatin resistance in human ovarian carcinoma cells through ATP-mediated lysosomal function. Int J Oncol. 2015;47:1890–900.
Karantza-Wadsworth V, White E. Role of autophagy in breast cancer. Autophagy. 2007;3:610–3.
Rudel S, Wang Y, Lenobel R, Korner R, Hsiao HH, Urlaub H, Patel D, Meister G. Phosphorylation of human Argonaute proteins affects small RNA binding. Nucleic Acids Res. 2011;39:2330–43.
Acar HYc, Garaas RS, Syud F, Bonitatebus P, Kulkarni AM. Superparamagnetic nanoparticles stabilized by polymerized PEGylated coatings. J Magn Magn Mater. 2005;293:1–7.
Abràmoff MD, Magalhães PJ, Ram SJ. Image processing with ImageJ. Biophotonics Intern. 2004;11:36–42.
Nair AB, Jacob S. A simple practice guide for dose conversion between animals and human. J Basic Clin Pharm. 2016;7:27–31.
Drost R, Dhillon KK, van der Gulden H, van der Heijden I, Brandsma I, Cruz C, Chondronasiou D, Castroviejo-Bermejo M, Boon U, Schut E, et al. BRCA1185delAG tumors may acquire therapy resistance through expression of RING-less BRCA1. J Clin Invest. 2016;126:2903–18.
Vassilopoulos A, Xiao C, Chisholm C, Chen W, Xu X, Lahusen TJ, Bewley C, Deng CX. Synergistic therapeutic effect of cisplatin and phosphatidylinositol 3-kinase (PI3K) inhibitors in cancer growth and metastasis of Brca1 mutant tumors. J Biol Chem. 2014;289:24202–14.
Y.A. was supported by a TUBITAK-BIDEB 2211 scholarship for Ph.D. studies. The SKBR3 and MDA-MB-453 cell lines were a kind gift of Huveyda Basaga. We also would like to thank Tugba Bagci-Onder and Ahmet Cingoz for technical help in IVIS imaging analyses, Cihan Taskin and Ahmet Kocabey for technical help in mice experiments and for blood count and blood biochemistry analyses. The authors declare that they have no conflict of interest.
This work was supported by the Scientific and Technological Research Council of Turkey (TUBITAK) 1003 Grant number 213M669 and Koc University.
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All animal experiments were approved by the Ethics Committee of the Koç University in accordance with the guidelines on animal care and use (File No: 2013-3).
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AGO2 protein binding improved MIR376B were abilized. (a) Overexpression of flag-AGO2 protein in HEK293T cells for 48 h and immunoprecipitation efficiency determined by pre- and flag-IP using flag antibody. p3Xflag was used as control transfection. (b) Comparative Taqman qPCR analysis of immunoprecipitated amount of MIR376B by RNA isolation from flag beads incubated with cell lysate of HEK293T cells with or without flag-AGO2 overexpression. (c) Determination of MIR376B level on flag-beads after 21 days of flag-AGO2 immunoprecipitation at room temperature by RNA isolation and Taqman qPCR. Taqman qPCR data was normalized using U6 small nuclear 1(RNU6-1) (U6) mRNA levels. Figure S2. Characterization of nanoparticles. (a) Zeta potential of SP-AH in PBS buffer (pH: 7.4) (b) Powder XRD pattern provided with the peak assignments of SP. (c) Thermogram of SP and PAA. (d) FTIR spectra of bare SPION, pure PAA and SP. Figure S3. (a) Measurement of AGO2 concentration of SP-A by Bradford assay. Standard curve generated from the absorbance of BSA at 595 nm as a function of BSA concentration (µg/mL). (b) Photoluminescence (PL) spectra of Dylight 650® at decreasing concentrations (2 × 10−2), 1 × 10−2, 4 × 10−2, 2 × 10−3, 1 × 10−3, 5 × 10−4 µM, λex: 655 nm, inset: Calibration curve of PL intensity vs concentration of DyLight 650®. PL spectra of (c) SP-AH (d) SP-F and (e) SP-AF. (λex: 655 nm, dilution factor: 20). Figure S4. Biocompatibility of SP and SP-AH nanoparticles in vitro and in vivo systems. (a) Determination of viability of 3 different breast cancer cells, MCF7, SKBR3 and MDA-MB-453, treated with increasing concentrations (5-500 µg/ml) of SP or SP-AH nanoparticles for 48 h by MTT cell viability assay. (b) Body weight change after 10 and 40 days in mice i.v. injected with SP, SP-AH (10 mg Fe per kg of mice) or equal volume of PBS. (c) Hematoxylin and eosin staining of mice tissues after 40 days of PBS, SP and SP-AH injections. Figure S5. Uptake and biodistribution of SP-AH nanoparticles in mice. (a) Iron amount in different mice tissues and tumor measured by Inductively Coupled Plasma (ICP) analysis one day after i.v. injection of PBS or SP-AH (10 mg Fe per kg of mice). (b) Ex vivo IVIS images of organs after one day of PBS or SP-AH i.v. injections. Figure S6. Determination of SP-AH nanoparticles on microRNA level in vitro. (a, b) QPCR analysis of SP-AH (150 µg/ml) treatment on MIR376B and its targets, BECN1 and ATG4C, after 48 h of treatment in SKBR3 (a) and MDA-MB-453 (b) cells. Control (CNT) cells were treated with equal amount of PBS with SP-AH treatment. QPCR data was normalized using U6 small nuclear 1 (RNU6-1) mRNA for MIR376B and GAPDH for ATG4C and BECN1 mRNAs. (mean ± SD of independent experiments, n = 3, *p < 0.05). Figure S7. Characterization of synthesized nanoparticles. (a) STEM micrograph of SP (b) Elemental analysis of SP showing the Fe and O (Scale bar: 20 nm). Figure S8. Full blot images of representative experiments that were presented in the manuscript. (a-e) Corresponding Figure numbers were marked. Processed areas were shown in a rectangle. Figure S9. HER2 status analysis by anti-HER2 antibody staining of MCF-7 and MDA cells. (a) Graphic demonstration and (b) FACS quadrant of HER2 positivity by FACScan. (c) Confocal imaging of SP-AH (150 µg/ml) treated MCF-7 and MDA cells. Scale bar: 25 µm. Figure S10. Comparative analysis of different aged SP-AH NPs. (a) Freshly prepared, (b) 6 month aged, (c) 1 year aged NPs analyzed. Lower part: Confocal imaging of targeting capacity; Upper part: QPCR analysis of MIR376B target BECN1 level after 48 h of treatment of SP-AH (150 µg/ml) in MDA-MB-453 cells. Scale bar: 25 µm. Figure S11. SP-AH/MIR376B nanoparticles anti-cancer effect on breast cancer cell lines. Viability of SKBR3 and MDA cells following the treatment with SP-AH, Cisplatin or SP-AH/MIR376B (n = 3, n.s.; not significant).
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Unal, O., Akkoc, Y., Kocak, M. et al. Treatment of breast cancer with autophagy inhibitory microRNAs carried by AGO2-conjugated nanoparticles. J Nanobiotechnol 18, 65 (2020). https://doi.org/10.1186/s12951-020-00615-4