Nanomicelles potentiate histone deacetylase inhibitor efficacy in vitro

Amphiphilic block copolymers used as nanomicelle drug carriers can effectively overcome poor drug solubility and specificity issues. Hence, these platforms have a broad applicability in cancer treatment. In this study, Pluronic F127 was used to fabricate nanomicelles containing the histone deacetylase inhibitor SAHA, which has an epigenetic-driven anti-cancer effect in several tumor types. SAHA-loaded nanomicelles were prepared using a thin-film drying method and characterized for size, surface charge, drug content, and drug release properties. Loaded particles were tested for in vitro activity and their effect on cell cycle and markers of cancer progression. Following detailed particle characterization, cell proliferation experiments demonstrated that SAHA-loaded nanomicelles more effectively inhibited the growth of HeLa and MCF-7 cell lines compared with free drug formulations. The 30 nm SAHA containing nanoparticles were able to release up to 100% of the encapsulated drug over a 72 h time window. Moreover, gene and protein expression analyses suggested that their cytoreductive effect was achieved through the regulation of p21 and p53 expression. SAHA was also shown to up-regulate E-cadherin expression, potentially influencing tumor migration. This study highlights the opportunity to exploit pluronic-based nanomicelles for the delivery of compounds that regulate epigenetic processes, thus inhibiting cancer development and progression.

is approved by the FDA for the treatment of malignant cutaneous T-cell lymphoma (CTCL) (Kawamata et al. 2007). Subsequently, it was found to offer therapeutic potential for other cancer types including cervical and breast (Prestegui-Martel et al. 2016;Shi et al. 2017) where female breast cancer represents around 30% of all new cancer cases in the US yearly, while uterine and cervical cancer make up to 7% of the total (Siegel et al. 2020). The use of MCF-7 and HeLa for breast and cervical cancer studies involving epigenetic drugs is well established due to the high genetic variability of these cells lines that could be tackled by such an approach (Landry et al. 2013;Zhou et al. 2019).
SAHA is a histone deacetylase (HDAC) inhibitor that can mediate the down-regulation of DNA transcription in numerous biological processes (Haberland et al. 2009) including cell growth arrest, activation of the extrinsic and intrinsic apoptotic pathways, autophagic, reactive oxygen species (ROS)-induced cell death, and mitotic cell death (Xu et al. 2007;Ververis et al. 2013;Zhang and Zhong 2014). Limitations in SAHA utility include low bioavailability, short half-life, and toxic side-effects, which are partly linked to the development of multidrug resistance (Bravo-Cordero et al. 2012;Friedl et al. 2012;Chung et al. 2013). Together, these factors have limited the clinical use of SAHA as an effective anti-cancer treatment (Konsoula and Jung 2008;Qi et al. 2017). Encapsulating SAHA within nanoparticles represents a potential strategy for overcoming such limitations to enhance its utility in clinic.
Nanoparticles including liposomes (Lee 2020), bio-nanocapsules (Tsutsui et al. 2007), and polymeric nanoparticles (El-Say and El-Sawy 2017) are being developed to overcome poor solubility and drug efficacy (Zhu and Liao 2015). Due to the unique physiological and pathological features of the tumor site, correctly sized nanomicelles can be passively targeted due to the enhanced permeability and retention (EPR) effect, which can improve the drug efficacy and reduce toxic side-effects (Fang et al. 2011;Zhu et al. 2016;Russo et al. 2016). Nanomicelles possess unique advantages including structural stability and simplicity of fabrication in a 10-100 nm size range (Tran et al. 2014;Kwak et al. 2015). They can also effectively prolong the retention time of drugs in vivo and prevent drug inactivation by enzyme degradation before reaching the tumor site (Biswas et al. 2013).
Pluronic is a water-soluble amphiphilic molecule with a poly(oxyethylene)-block-poly (oxypropylene)-block-poly(oxyethylene) (PEOx-PPOy-PEOz) triblock structure (Farrugia et al. 2014), which self-assembles forming core-shell micelles in aqueous media. For instance, chlorpromazine (CPZ)-containing Pluronic nanomicelles have been shown to enhance the cytotoxicity of the drug and increase its selectivity towards chronic myeloid leukemia cells, demonstrating the pharmacological potential for cancer treatment (Mello et al. 2016). Moreover, Solasodine, a type of steroidal alkaloid that exhibits excellent bioactivities against fungi, viruses, and especially tumors, has been encapsulated into Pluronic F127 nanocarriers, and was able to enhance the anti-cancer effect of Solasodine alone in A549 and Hela cells (Zhang et al. 2015). A similar approach has also been used for doxorubicin hydrochloride-loaded pluronic F127 nanocapsules which demonstrated delayed drug release (Zeng et al. 2014).
Here, we showed that the HDAC inhibitor SAHA can be efficiently loaded into pluronic F127 nanomicelles. We demonstrate that SAHA-loaded nanomicelles are able to efficiently release the drug in a time-dependent fashion. SAHA nanomicelles were shown to be more efficient than the free drug in reducing cell viability and inhibiting cell migration capacities of breast and cervical cancer cell lines, which represent two cancer types that still require more effective, epigenetic-based, treatments. Cellular uptake studies demonstrated the effective micellular uptake and intracellular distribution in a cell linedependent fashion. In addition, the encapsulated SAHA remained effective in triggering cell cycle arrest and apoptosis in a dosage-dependent manner. The HDAC inhibitor also altered the expression of the EMT markers E-cadherin and N-cadherin, suggesting that effective delivery has the potential to reverse the aggressive, metastatic phenotype of these cancer models.

Preparation of SAHA-pluronic F127 nanoparticles
200 mg of Pluronic F127 and 3 mg of SAHA were dissolved into 10 ml of acetonitrile. Subsequently, the solvent was removed by rotary evaporation at 55℃ with decompression. The solid copolymer matrix obtained was then preheated at 65℃ for 1 h and eventually hydrated with phosphate buffer solution (PBS, 10 mM or 150 mM NaCl) or H 2 O. The nanomicellar solution was filtered with a 0.22 μm filter to remove any free drug. PI encapsulation was similarly achieved. 10 mg PI and 200 mg were dissolved in 10 ml of acetonitrile, and followed the same process explained above. The dispersion, size, and zeta potential of nanomicelles were measured by dynamic light scattering (Particle size analyzer, Malvern, UK).

Atomic force microscope (AFM) characterization
10 μL of nanomicelle aliquots were spotted on mica substrates at a concentration of 100 μg/mL (Agar Scientific, UK) and dried at room temperature. Sample topography was obtained in air using a Bruker BioScope Catalyst (Bruker Instruments, Santa Barbara, California, USA) AFM. Bruker ScanAsyst-Air cantilevers were used, with a nominal spring constant of 0.4 N/m and a nominal resonant frequency of 70 kHz. All imaging was conducted using Peak Force Tapping (PFT) in ScanAsyst Mode. Images were processed with first-order flattening and planefit using Bruker Nanoscope Analysis 1.5. Gwyddion in-built grain analysis was used to identify nanomicelles and to calculate their size.

Drug release assessment
A high-performance liquid chromatography (HPLC) system (Waters 2535, Milford, MA, US) equipped with a photodiode array detector was used for the analysis of the drug release potential of the pluronic formulations. A C18 HPLC column (Grac-eSmart RP C18, 4.6 mm × 250 mm, 5 μm) was used for quantitative analysis of SAHA. Mobile phase A contained HPLC grade H 2 O, and mobile phase B contained HPLC grade acetonitrile. SAHA was eluted with 50% mobile phase A and mobile phase B at a flow rate of 1 ml/min, with a retention time of 3.6 min and UV detection at 265 nm. Standard curves of concentration peaks and areas were drawn. Five-point calibration curves for SAHA in the range of 31.25-500 μM were considered reliable (r 2 ≥ 0.999).

Determination of drug loading and entrapment efficiency.
200 μl of nanomicelle solution were added with 800 μl acetonitrile and centrifuged for 5 min at 10,225×g. The supernatant was used to determine the concentration of drug by HPLC.
The entrapment efficiency (EE) and drug loading efficiency (DL) were calculated as follows:

In vitro drug release
To measure the release of SAHA from nanomicelles, a 20 ml solution containing SAHA-loaded nanomicelles was loaded into a dialysis bag (MWCO: 8000 ~ 14,000 Da, Spectrum ® , Rancho Dominquez, CA, USA), which was immersed in 500 ml of 10 mM PBS (pH 7.4). Temperature was maintained at 37 °C. At predetermined time intervals, 1 mL of release medium (PBS) was withdrawn and replaced with the same volume of fresh PBS into the system. The concentration of SAHA inside the solution was determined by HPLC.

Cell lines
HeLa (human epithelial cervical cancer) and MCF-7 (human breast adenocarcinoma) cell lines were kindly donated by Suzhou Institute of Nano-Tech and Nano-Bionics (SINANO), Chinese Academy of Sciences. HeLa cells were grown in DMEM and MCF-7 cells in RMPI. All media was supplemented with penicillin (100 U/ml) and

DL% =
Weight of drug in nanomicelles Weight of drug loaded nanomicelles * 100% EE% = Weight of drug in nanomicelles Weight of drug added into nanomicelles * 100%.

Protein blot
2.5 × 10 5 cells were dispersed in three 6-well plates, grown overnight, and three plates treated with SAHA, SAHA nanomicelles and empty nanomicelles for 24 h or 48 h. The cells were lysed in RIPA lysis buffer containing protease and phosphatase inhibitors (Beyotime, China) and total protein was estimated with BCA Protein Assay Kit (Beyotime, China). Protein was separated by SDS-PAGE and transferred on PVDF membranes (Beyotime, China). The membranes were blocked in 5% skimmed milk, incubated with primary antibodies for p21, p53, N-Cadherin or E-cadherin (Santac Cruz, US), and then incubated with the appropriate HRP conjugated secondary antibody (Absin, China).

Quantitative RT-PCR (qRT-PCR)
Hela and MCF-7 cells were treated with the SAHA and SAHA-loaded nanomicelles for 24 h or 48 h. Total RNA was isolated using the RNAiso Plus kit (Takara, Japan). 10 μg of total RNA was converted into complementary DNA (cDNA) with PrimeScript RT reagent kit with gDNA Eraser (Takara, Japan). SYBR Premix Ex TaqTMII (Takara, Japan) solution was used according to the manufacturer's protocol to measure for mRNA expression of p53, p21, E-cadherin and N-cadherin with by qPCR. GAPDH was used as a control to determine relative mRNA expression. The table below shows the primer sequences used. Cellular uptake of nanomicelles 1.5 × 10 4 HeLa and MCF-7 cells/well were seeded in 8-well chambered coverslips (Ibidi). After 24 h from seeding, cells were treated with 1 µM of PI-loaded pluronic F127 nanoparticles and incubated at 37 °C in a humidified atmosphere. PBS was added as the untreated control. After 4 h, 24 h, and 48 h, cells were washed with 1X PBS and nuclei were counterstained with Hoechst 33342 (Life Technologies). 0.1% Triton-X-100 was used as a positive control and added to cells for 10 min to permeabilize them, followed by 1 µM PI treatment for 10 min. Cells were imaged live on a Zeiss LSM710 fluorescent confocal microscope (Carl Zeiss Microscopy, Jena) at a 40X magnification using the 543 nm and 405 nm laser lines.

Cell migration assay
MCF7 and HeLa cells were seeded at a 5 × 10 5 cells/well concentration in 6-well plates. When cells reached 90% confluence scratches were performed with a 200 µl sterile pipette tip and detached cells were washed in 1× PBS. Subsequently, empty nanomicelles, SAHA nanomicelles, and free SAHA were added to each well, and the final volume was brought to 2 ml with FBS-free media. Images were acquired at 0 h, 24 h, and 48 h using a Zeiss inverted microscope at a 4× magnification.
Reference marks on the bottom of each well along the scratches were made to align the same fields in each image acquisition, at each time point. Image analysis of the scratches was performed using the Wound Healing Size Tool, an ImageJ/Fiji ® plugin that allows for the quantification of the wounded area (Suarez-Arnedo et al. 2020). The scratch area was calculated for each field and time point, and the percentage of wound closure was calculated according to the following formula: where A t=0 is the area of a specific field at time 0 h and A t=Δt is the area of the same field after n hours of the initial scratch. The data were graphed and analyzed using GraphPad Prism. For the statistical analysis, it was used one-way ANOVA with Dunnett's multiple comparison test.

Statistical analysis
Data were expressed as mean ± standard deviation and analyzed using SPSS software. According to the distribution type of the data, the samples were processed by T test and one-way ANOVA analysis with Dunnett's multiple comparison test. A p value p < 0.05 was considered statistically significant.

Characterization and assessment of stability of SAHA-loaded nanomicelles over time
Nanomicelles were fabricated using a thin-film method and characterized by dynamic light scattering. Empty and SAHA-loaded nanomicelles both had an average size of 23 nm and a poly-dispersive index (PDI) of 0.09 ± 0.02 and 0.08 ± 0.0, respectively, confirming the uniformity of distribution of the formulation (Table 1). The surface charge of the particles was measured with a Zetasizer Nano instrument (Malvern, UK), providing a zeta-potential value of − 1.28 ± 0.28 mV. The entrapment efficiency (EE%) and drug loading efficiency (DL%) values were 94.36 ± 0.76% and 1.31 ± 0.062%, respectively. Particles were imaged using Atomic Force Microscope (AFM) and identified using the grain analysis algorithm in Gwyddion (Kohn et al. 2018). Nanomicelles showed a rounded shape and both empty (Fig. 1a) and SAHA-loaded (Fig. 1b) nanomicelles presented a diameter of 32 nm. Both AFM and DLS experiments confirmed that no change was detectable in micelles dimensions upon incorporation of the drug. To determine nanomicelle stability, particle size was evaluated in three different solutions (H 2 O, 10 mM PBS and 150 mM PBS) at different time points for up to 30 days (Fig. 2). In all three solutions, the initial particle size of SAHA nanomicelles was 30 nm. In H 2 O, the micelles aggregated over time, increasing six-fold in size compared to day 0 (Fig. 2a). Less aggregation was observed in 10 mM PBS (Fig. 2b), and no aggregation was observed for nanomicelles in PBS-containing physiological NaCl concentrations (150 mM, Fig. 2c). PBS (150 mM NaCl) was, therefore, selected for all further experiments.

Sustained release profiling
SAHA-loaded nanomicelles were analyzed for their capacity to sustain SAHA release over time (Fig. 3). SAHA was retained for a longer period of time when loaded in nanomicelles with only 36.53% ± 3.43 of drug released after 2 h and 85.68% ± 2.48 after 72 h, compared to free SAHA where levels reached 51.55% ± 1.56 after 2 h, 96.27% ± 3.47 after 72 h. In vitro drug release of SAHA from nanomicelles. Nanomicelles encapsulated with SAHA and resuspended in PBS were tested for their capacity to release the drug over time. HPLC was used to measure the amount of SAHA released after up to 72 h. The ± SD value of the data was tested by T test (n = 3)

Nanomicelles cellular uptake
To understand the mechanisms of nanomicelle uptake, HeLa and MCF-7 cells were exposed to F127 nanomicelles loaded with the fluorescent dye propidium iodide (PI). Cellular uptake was assessed at 4 h, 24 h and 48 h time points. Nanomicelle uptake by HeLa cells was measured by confocal microscopy at two different concentrations, 0.1 μM and 1 μM (Fig. 4). Treatment with 0.1 μM nanomicelles yielded a noticeable PI uptake after 48 h, while the PI signal could already be visualized after 4 h following exposure to 1 μM PI nanomicelles, where a clear co-localization signal was observed in the cell nuclei (blue, Fig. 4).
Treatment of MCF-7 cells with PI nanomicelles resulted in a different temporal cellular uptake pattern compared to HeLa cells (Fig. 5). Treatment with 0.1 μM PI nanomicelles resulted in particle localization at the peri-nuclear zone after 24 h, and localization within the nuclei after 48 h, showing the intracellular transport of these particles to the nucleus can be accomplished using the delivery system. At higher treatment concentrations (1 μM), particles reached the cell nuclei after only 4 h from the addition and yielded the highest signal after 48 h.

SAHA-loaded nanomicelles inhibit Hela cell and MCF-7 cell proliferation
The ability of SAHA-loaded nanomicelles to inhibit cell proliferation in both Hela and MCF-7 cancer cell lines was assessed. HeLa and MCF7 cell lines were treated with 1 μM and 5 μM of free drug or SAHA-encapsulated nanoparticles for up to 72 h. The 1 μM  (Fig. 6a, c), while the nanomicelles became significantly more effective than the free drug after 72 h on HeLa cells (p < 0.05). Conversely, the 5 μM concentration of SAHA-encapsulated nanomicelles proved to be more effective than the free drug after 48 h for both HeLa (p < 0.05, Fig. 6b) and MCF7 (p < 0.01, Fig. 6d). The same trends were maintained after 72 h of exposure to the treatment for both HeLa and MCF7 cells. These observations suggested that nanomicelle encapsulation of SAHA serves to enhance its cytotoxicity.

Effect of SAHA-loaded nanomicelles on cell cycle and EMT
To evaluate the effect of SAHA encapsulation on the expression of p21 and p53 (cell cycle markers) and E/N-cadherins (EMT markers), HeLa cells were treated with free and encapsulated drug for 24 h and 48 h. Increasing concentrations of both free drug and SAHA-encapsulated nanomicelles led to a significant up-regulation of p21 (p < 0.05) and a down-regulation of p53 (p < 0.05) at both 24 h (Fig. 7a, b) and 48 h (Fig. 7d-e). Moreover, SAHA-loaded nanomicelles were more effective than free SAHA (p < 0.05) in triggering alterations at the protein level (Figs. 7a, 4b), and this effect was corroborated by mRNA expression analysis of the same markers (Figs. 7c, 4f ), with SAHA-loaded nanomicelles having a significantly greater effect on the expression of p21 and p53 mRNA (p < 0.01) than free drug. The effect of SAHA and SAHA-loaded nanomicelles on The effect of SAHA encapsulation in metastatic processes was undertaken by determining the expression patterns of E-cadherin and N-cadherin. After 24 h, SAHA and SAHA-loaded nanomicelle treatement resulted in a significant up-regulation of E-cadherin protein in Hela cells (p < 0.05) (Fig. 7c). Similarly, the 48 h treatment with either SAHA and SAHA nanomicelles resulted in significantly increased E-cadherin expression (p < 0.05) (Fig. 7f ). SAHA-encapsulated nanoparticles were more effective than free drug in increasing E-cadherin levels. However, neither SAHA nor SAHA-loaded nanomicelles had an effect on N-cadherin expression.
The same analysis was performed on MCF-7 cells, which displayed a similar response to Hela cells after 24 h treatment, with both SAHA and SAHA-loaded micelles significantly up-regulating p21 and down-regulating p53 protein (Fig. 8a) and mRNA expression levels (Fig. 8b). The same trend was seen after 48 h (Fig. 8d-e). Furthermore, SAHA-loaded nanomicelles exhibited a greater effect on protein expression on both targets compared to free SAHA (p < 0.05). Furthermore, gene expression analysis showed a significant increase in E-cadherin and decrease in N-cadherin after 24 h (Fig. 8c), which was maintained after 48 h for E-cadherin only (Fig. 8f ). In general, SAHA-encapsulated nanoparticles were more effective in increasing the levels of E-cadherins than the free drug. Expression of all four markers was analyzed by western blot at 24 h (a) and 48 h (d). Data were normalized to the level of GAPDH. The effect of SAHA and SAHA-loaded nanomicelles on p21 and p53 mRNA expression was also done at 24 h (b) and 48 h (e), and normalized to the level of GAPDH, while the E-and N-cadherin mRNA analysis at 24 h and 48 h is shown in (c) and (f), respectively. The expression level is shown relative to the control as 1. A t test to test for statistical significance was performed (*p < 0.05, **p < 0.01, ***p < 0.001) Analysis of cell migration capacity following SAHA nanomicelle exposure 0.1 μM SAHA nanomicelles were assessed for their ability to inhibit HeLa and MCF-7 cell growth and migration using a wound-healing assay. Following treatment for 24 h and 48 h, a time-dependent effect of the treatment on HeLa cell division and inhibition of migration was observed (Fig. 9a). After 24 h, both SAHA nanomicelles and SAHA were found to inhibit wound closure compared to empty nanomicelles (p < 0.01 and p < 0.05 respectively, Fig. 9b). After an extended 48 h treatment period, the negative effect of SAHA nanomicelles on wound closure was more marked than the free drug, which surprisingly was even less effective than the empty nanomicelle treatment (p < 0.001, Fig. 9c).
Similarly, when MCF-7 cells were exposed to 0.1 μM SAHA nanomicelles, a clear decrease in wound-healing capacity was observed after 24 h (Fig. 10a, b). Moreover, this effect was more enhanced after 48 h, where SAHA-nanomicelles yielded the most marked reduction in wound closure (p < 0.001) compared to SAHA only (p < 0.05, Fig. 10c).

Discussion
Here, we have demonstrated that the histone deacetylase inhibitor SAHA can be effectively encapsulated in pluronic nanoparticles. We confirmed, by means of dynamic light scattering and AFM analysis, that the size and phenotype of nanomicelles did not change upon SAHA encapsulation.
As SAHA has been shown to cause harmful side-effects, analysis of the amount of encapsulated drug within the nanomicelles was undertaken, as encapsulation could be an effective route to reducing systemic toxicity. Reported side-effects include fatigue, GI related diarrhea, nausea, thrombocytopenia, and anorexia as observed in different types of cancers, including endometrial cancers and lymphomas (Takai et al. 2004;Duvic 2008).

Fig. 9
Effect of SAHA-loaded nanomicelles on the wound closure capacity of HeLa cells. Representative microscope images (Fig. 10a) and analysis (Fig. 10b) of the wound closure. Wound closure capacity values are shown relative to the empty nanomicelles control. A one-way ANOVA with Dunnett's multiple comparison test for statistical significance was performed (*p < 0.05, **p < 0.01, ***p < 0.001) Drug release experiments showed that SAHA was progressively released from pluronic nanomicelles for up to 72 h. These results were complemented by the analysis of the uptake of nanomicelles by breast and cervical cancer cell lines MCF-7 and HeLa, which showed a time-dependent nanomicelle uptake that was more enhanced in the MCF-7 cell line after 48 h. This effect could be due to different intracellular uptake patterns of nano-encapsulated formulations by different cell types. Indeed, the majority of free drugs enter cells through a simple diffusion process, while most nanocarrier drugs enter cells through endocytosis (Kumari et al. 2016;Behzadi et al. 2017;Foroozandeh and Aziz 2018). These findings are in line with the previous reports that showed the efficient employment of pluronic F127 for the encapsulation and cellular uptake of compounds, such as curcumin (Wang et al. 2015;Vaidya et al. 2019), paclitaxel (Nie et al. 2011), and doxorubicin (Manaspon et al. 2012).
Experiments showed that nanomicelle-encapsulated SAHA was more effective than the free drug in causing cell death. This effect was most evident after 72 h, suggesting a sustained release of SAHA over time. Encapsulation could, therefore, result in the use of less drug while still obtaining the required therapeutic effect, or in the more effective and tumor site specific delivery due to the inherent properties of nanostructures. A wound-healing assay further demonstrated the effectiveness of SAHA nanomicelles over longer time periods for HeLa and MCF-7 cells, with a slightly different effect observed with each cell line. Indeed, the fact that breast cancer cells were more susceptible to the effect of SAHA nanomicelles than cervical cancer cells might provide insights for future therapeutic approaches.
SAHA treatment caused significant changes in proteins involved in both cell cycle and cell phenotype. We demonstrated that SAHA-loaded nanomicelles were able to up-regulate p21 and down-regulate p53 expression, consistent with the previous studies on the action of free SAHA on tumor growth inhibition by regulating the expression of these genes (Davies et al. 2015;Ogata et al. 2017).

Fig. 10
Effect of SAHA-loaded nanomicelles on the wound closure capacity of MCF7 cells. Representative microscope images (a) and analysis (b) of wound closure. Wound closure capacity values are shown relative to the empty nanomicelles control. A one-way ANOVA with Dunnett's multiple comparison test for statistical significance was performed (*p < 0.05, **p < 0.01, ***p < 0.001) Detailed analysis of the effects of SAHA-loaded nanoparticles on EMT transition markers revealed a significant up-regulated E-cadherin expression, but with no affect N-cadherin expression. This is consistent with previous studies, where HDAC inhibitors were shown to have only a slight effect on N-cadherin expression in HT-144 and A375 cells (Díaz-Núñez et al. 2016). Down-regulation or loss of E-cadherin expression affects cadherin-catenin complex formation and stability, which directly affects the metastatic process (Zhang et al. 2000;Guo et al. 2018). It has been suggested that SAHA may inhibit the formation of Snail and HDAC1/HDAC2 complexes by inhibiting the activity of HDAC1 and HDAC2, leading to the demethylation and transcriptional activation of the E-cadherin. In addition, SAHA may also up-regulate E-cadherin expression by altering its upstream targets (LEF-1 and Slug) (Nalls et al. 2011), but the specific mechanisms need to be further elucidated.

Conclusions
Encapsulation of SAHA into nanomicelles enhances the potency of this epigenetic drug in breast and cervical cancer cell models. Furthermore, this effective formulation will likely enhance drug delivery to tumor sites, and overcome current issues in delivering HDAC inhibitors to solid tumors, while also reducing side-effects associated with systemic delivery of the free drug. The EPR effect would enable these nanoparticles to escape via neo-vascularization at tumor sites, and subsequently, their physico-chemical characteristics would allow better penetration into solid tumors (Blanco et al. 2015;Zhang et al. 2019). Such parameters are likely to be specific to different cancer types, and indeed, we observed that the SAHA-loaded nanomicelles displayed different uptake rates, and directed intracellular trafficking in the two different cancer cell models tested here (Figs. 4,5).