Polymer coated gold-ferric oxide superparamagnetic nanoparticles for theranostic applications

Background Engineered inorganic nanoparticles (NPs) are essential components in the development of nanotechnologies. For applications in nanomedicine, particles need to be functionalized to ensure a good dispersibility in biological fluids. In many cases however, functionalization is not sufficient: the particles become either coated by a corona of serum proteins or precipitate out of the solvent. We show that by changing the coating of magnetic iron oxide NPs using poly-l-lysine (PLL) polymer the colloidal stability of the dispersion is improved in aqueous solutions including water, phosphate buffered saline (PBS), PBS with 10% fetal bovine serum (FBS) and cell culture medium, and the internalization of the NPs toward living mammalian cells is profoundly affected. Methods A multifunctional magnetic NP is designed to perform a near-infrared (NIR)-responsive remote control photothermal ablation for the treatment of breast cancer. In contrast to the previously reported studies of gold (Au) magnetic (Fe3O4) core–shell NPs, a Janus-like nanostructure is synthesized with Fe3O4 NPs decorated with Au resulting in an approximate size of 60 nm mean diameter. The surface of trisoctahedral Au–Fe3O4 NPs was coated with a positively charged polymer, PLL to deliver the NPs inside cells. The PLL–Au–Fe3O4 NPs were characterized by transmission electron microscopy (TEM), XRD, FT-IR and dynamic light scattering (DLS). The unique properties of both Au surface plasmon resonance and superparamagnetic moment result in a multimodal platform for use as a nanothermal ablator and also as a magnetic resonance imaging (MRI) contrast agent, respectively. Taking advantage of the photothermal therapy, PLL–Au–Fe3O4 NPs were incubated with BT-474 and MDA-MB-231 breast cancer cells, investigated for the cytotoxicity and intracellular uptake, and remotely triggered by a NIR laser of ~ 808 nm (1 W/cm2 for 10 min). Results The PLL coating increased the colloidal stability and robustness of Au–Fe3O4 NPs (PLL–Au–Fe3O4) in biological media including cell culture medium, PBS and PBS with 10% fetal bovine serum. It is revealed that no significant (< 10%) cytotoxicity was induced by PLL–Au–Fe3O4 NPs itself in BT-474 and MDA-MB-231 cells at concentrations up to 100 μg/ml. Brightfield microscopy, fluorescence microscopy and TEM showed significant uptake of PLL–Au–Fe3O4 NPs by BT-474 and MDA-MB-231 cells. The cells exhibited 40 and 60% inhibition in BT-474 and MDA-MB-231 cell growth, respectively following the internalized NPs were triggered by a photothermal laser using 100 μg/ml PLL–Au–Fe3O4 NPs. The control cells treated with NPs but without laser showed < 10% cell death compared to no laser treatment control Conclusion Combined together, the results demonstrate a new polymer gold superparamagnetic nanostructure that integrates both diagnostics function and photothermal ablation of tumors into a single multimodal nanoplatform exhibiting a significant cancer cell death. Electronic supplementary material The online version of this article (10.1186/s12951-018-0405-7) contains supplementary material, which is available to authorized users.


Background
Assembly of the hyperthermia property of superparamagnetic nanoparticles (NPs) with imaging function into a single nanostructure offers a promising way to dynamically monitor the progress of the disease and enhance therapeutic efficacy. Unlike single-component materials, which usually contain only one unique property of the active ingredient, the ingredients of multicomponent materials offer the possibility of multimodal application of these functional components thereby increasing versatility of these materials [1,2]. The development of multicomponent materials as theranostic nanosystems has a potential to establish a new therapeutic mode to combine imaging and hyperthermia, which can greatly increase the therapeutic efficacy with real-time monitoring in tissues. Normal tissues and tumors differ only slightly in relaxation time, and hence, cannot propagate proper diagnosis signals during magnetic resonance imaging (MRI) [3]. The development of new MRI contrast agents based on NPs is a fascinating field of research that focuses on improving MRI techniques for the early detection of disease. Superparamagnetic NPs such as ferric oxide (Fe 3 O 4 ) have been extensively employed as an MRI contrast agent [4][5][6][7][8][9][10], altering the magnetic resonance (MR) signals by reducing the relaxivity through de-phasing of the transverse magnetization [11,12]. A gold (Au) shell coating may be useful in this regard in order to enhance not only the imaging contrasts for MRI but also the photothermal effect via the plasmonderived optical resonances of gold shells in the visible and near-infrared region (NIR) [13]. The combination of Aucoated NPs has tremendous potential in improving optical properties, thermal properties, tunable geometry, and imaging contrasts in MRI. As a bifunctional NP, Au-Fe 3 O 4 can inherit excellent surface chemistry characteristics, unique optical properties (attributed to Au) and superparamagnetic characteristics attributed to Fe 3 O 4 . First of all, the NPs offer size controllability, ranging from few to hundreds of nanometers with different and unique size-dependent properties. Second, the NPs can be easily controlled and manipulated from outside with the help of external magnetic field being operated from a distance. Third, the NPs can provide enhanced contrast in medical imaging that can be used to diagnose the situation efficiently. These characteristics would enhance and broaden the application of these nanoparticles for theranostic applications.
While only a few number of Au and magnetic NPs have been approved for clinical and preclinical trials by the U.S. Food and Drug Administration (FDA) [14][15][16][17], toxicity of both coated and uncoated magnetic NPs remain a serious concern [18][19][20][21]. Both Au and Fe 3 O 4 NPs exhibit toxicity to cells via numerous mechanisms including the disruption of the cell membrane, DNA damage, induction of oxidative stress, generation of free radicals, impairment of mitochondrial function and alteration in cell signaling among others [22][23][24]. The toxicity may not be caused by single NP, but rather due to the aggregation of NPs in biological media and serum [25,26]. Given the unstable nature of NP formulation, it is hypothesized that an optimum dose of a cationic polymer coating onto Au-Fe 3 O 4 NPs play a role in determining NP configuration on cellular cytotoxicity as well as direct therapy. Coating the surface of Au-Fe 3 O 4 NPs with suitable polymers may offer several features: (i) reduced aggregation tendency of the particles; (ii) improved dispersibility; (iii) enhanced colloidal stability; (iv) protected undesirable surface oxidation; (iv) surface conjugation for targeting; (v) decreased cytotoxicity; and (vi) increased intracellular uptake by target cells. A charged polymer coating on the NP surface enhances the electrosteric stabilization by attractive and repulsive forces. Poly-l-lysine (PLL) is a biocompatible polycation that promotes cell adhesion by the presence of amine (-NH 2 ) groups [27][28][29]. PLL has been used to increase blood circulation, improve solubility as well as enhance MRI imaging contrasts of gadolinium imaging chelates [27,[29][30][31][32]. Steric stabilization has proven to be an effective method to improve NP colloidal stability in ionic media [33]. A uniform coating of Fe 3 O 4 NPs with polysaccharides leads to a decrease in saturation magnetization as compared to uncoated particles [34]. This drop in saturation magnetization is undesirable due to poor signaling in MRI imaging. Therefore, there is a need for a stable coating on the surface of Au-Fe 3 O 4 NPs to prepare a colloidal dispersion in the biological medium and attain high MRI imaging contrasts.
In this study, multifunctional Au-Fe 3 O 4 NPs were designed for medical imaging and hyperthermal treatments of breast cancer cells. To overcome the limitation of colloidal stability and low dispersity of NPs, a PLL polymeric coating was introduced to the surface of Au-Fe 3 O 4 as a physical barrier for preventing NP aggregation as well as enhancing their intracellular uptake by breast cancer cells. Our results showed that the PLL coating on Au-Fe 3 O 4 enhanced it stability in biological fluids such as water, phosphate buffered saline (PBS), cell culture medium and PBS containing 10% fetal bovine serum (FBS). PLL coated Au-Fe 3 O 4 NPs further enhanced the contrast of MRI imaging signals, exhibited intracellular uptake Keywords: Breast cancer, Combination treatments, Gold-superparamagnetic nanoparticles, Magnetic resonance imaging (MRI), Photothermal treatment, Polymer coating across the breast cancer cell membrane and decreased the cancer cell viability following photothermal treatment. The novelty of this work is to generate a nanometer-thick PLL layer for the stable dispersion of Au-Fe 3 O 4 NPs in biological fluids that results in excellent optical, magnetic and therapeutic properties for the cancer treatment.

Synthesis of Au-Fe 3 O 4 NPs
The Au-Fe 3 O 4 NPs were synthesized by a one-pot synthesis technique based on the method that has been published by Pariti et al. [35]. Briefly, the NPs were synthesized by injecting 2.5 mM of Fe(CO) 5 , 0.25 mM of HAuCl 4 , 2.5 mM oleic acid, and 2.5 mM of oleylamine into 5 ml of Triton ® X-100 at 85 °C. The reaction was conducted for 10 min in a three-neck round bottom flask equipped with a magnetic stir bar and air condenser. The temperature was increased to 300 °C. The product was a black precipitate that was isolated from the reaction mixture by magnetic filtration, followed by ultrasonication, centrifugation, and washing to remove excess Triton ® X-100 and any unreacted precursors. The powder collected at the bottom of the centrifuge tube was dried in air. The preparation of Au-Fe 3 O 4 NPs was confirmed by XRD analysis using a D/max-2400 diffractometer and CuK radiation (λ = 0.1541 nm).

Polymer coating on Au-Fe 3 O 4 NPs
To coat the NP surface with PLL, 660 µl of 0.1% ( w v ) PLL (Sigma Aldrich, MW: 150,000-300,000) was added to 25 mg of Au-Fe 3 O 4 NPs and incubated for 24 h at room temperature (~ 22°C) under continuous shaking. Unbound PLL was removed by centrifuging at 5000×g for 30 min that was repeated twice and measured using the trypan blue assay, spectrophotometry, and a standard curve (Additional file 1: Figure S1a) [36]. The concentration of Au-Fe 3 O 4 NPs was determined using a standard curve of the NP absorption at 710 nm peak (Additional file 1: Figure S1b). The mass ratio of PLL and NPs were calculated. The presence of PLL coating was confirmed by Fourier Transform Infrared (FT-IR) spectroscopy. The FT-IR spectrometer (Perkin-Elmer) was equipped with an electronic temperature control (ETC) EverGlo IR Source and a deuterated triglycine sulfate (DTGS) detector. FT-IR analysis was carried out for uncoated and PLL coated Au-Fe 3 O 4 NPs by mixing with potassium bromide (KBr) and a pellet method, after a baseline correction being made with dried KBr, to confirm the compatibility. The pellet was prepared to a pressure of about 5 × 10 6 Pa, in an evacuated chamber, to produce a clear transparent disc of diameter 2 cm and thickness of 0.2 cm. The spectra were recorded at room temperature (~ 25°C) from 4000 to 400 cm −1 .

Nanoparticle characterization
To measure the d mean of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs, transmission electron microscope (TEM) images were obtained using a Tecnai F20 at an accelerating voltage of 120 kV. A drop of 10 μl of each NP sample in water was air-dried on carbon-coated copper grids (Ted Pella). Images were recorded and analyzed using ImageJ (version 1.45S, NIH, USA) to calculate d mean for at least 20 particles. The size distribution of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs was determined by dynamic light scattering (DLS). The zeta potential was measured via laser Doppler anemometry using a Zetasizer Nano ZS (Malvern Instruments). Samples were prepared in water, PBS, RPMI 1640 cell culture medium and PBS with 10% FBS. Measurements were performed in triplicates and shown as the mean ± standard deviation (S.D.). The X-ray diffraction (XRD) patterns were performed by a Philips X-Pert X-ray powder diffractometer with CuKα (1.5418 Å) radiation from 5 to 90°. The UV-Vis absorption spectra of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs were measured using a Bio-Tek microplate reader (BioTek Synergy 2) between 400 and 900 nm. Fourier transform infrared (FT-IR) spectroscopy of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs was carried out using a Perkin Elmer Spectrum GX spectrophotometer. Thermal gravimetric analysis (TGA) was performed using a Q50 thermal gravimetric analyzer (TA instruments). The samples were heated from 25 to 1000 °C at a heating rate of 10 °C/min under N 2 flow. Results are expressed in weight percent as a function of temperature.

Spin-spin magnetic relaxation (T2 ms) studies of PLL-Au-Fe 3 O 4 NPs
To measure the relaxation variables in MRI, Au-Fe 3 O 4 NPs coated with PLL (PLL-Au-Fe 3 O 4 ) were prepared in water at 100 μg/ml concentration. All measurements were conducted at 37 °C using a Bruker's magnetic relaxometer mq20 (0.47 T, B = 20 MHz) for the spin-spin magnetic relaxation time (T 2 ) experiments. The specimens were dispersed in PBS and PBS containing 10% FBS at different Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NP concentrations (1, 10 and 100 μg/ ml). The proton spin-spin magnetic relaxation time, T 2 was measured as a function of the NP concentration.

Cytotoxicity of PLL-Au-Fe 3 O 4 NPs in Breast Cancer Cells
BT-474 and MDA-MB-231 breast cancer cells (ATCC) were cultured at 37 °C and 5% CO 2 in Hybri-Care (ATCC) and RPMI 1640 (Life Technologies), respectively supplemented with 10% FBS (Corning) and 1% (100 units/ml) Penicillin-Streptomycin (Gibco). Cells in the exponential growth phase were seeded in a 96-well plate at an initial density of 10,000 cells/well and incubated overnight. Different concentrations of PLL-Au-Fe 3 O 4 NPs (0-500 μg/ ml) were added to the cell culture media. After 2 h of incubation, the media was removed, and the cells were washed using PBS followed by re-incubation in cell culture media for additional 72 h. The viable and dead cells were measured using a live-dead (calcein AM; CAM and EthD-1) assay (Invitrogen) and calculated according to the manufacturer's protocol. The cells without any NP treatments were used as the control. The percentage cell death was calculated by the following equation: where F NPs is the Ethd-1 fluorescence of the cells treated with PLL-Au-Fe 3 O 4 NPs, F blank is the Ethd-1 fluorescence of the cell culture medium alone, and F control is the Ethd-1 fluorescence of the cells without any NP treatments. The concentration at which cell death was less than 10% was identified as a non-toxic dose.

Intracellular uptake of PLL-Au-Fe 3 O 4 NPs
Cellular uptake of PLL-Au-Fe 3 O 4 NPs was observed using a Carl Zeiss Axio observer Z1 research microscope system with Apotome.2 optical structuring device. BT-474 and MDA-MB-231 cells were seeded in 8-well chambers containing 10,000 cells/well and grown until 70% confluence. PLL-Au-Fe 3 O 4 NPs of 100 μg/ml were added to the wells, incubated for 2 h, and washed using PBS for three times. Live cells were re-incubated with media and imaged on a Zeiss microscope using a 63× objective (water) through phase contrast. The intracellular uptake of PLL-Au-Fe 3 O 4 NPs by BT-474 and MDA-MB-231 cells were further examined by TEM at a voltage of 80 kV. Briefly, cells were seeded in T25 flasks at a density of 1 × 10 6 cells/ml. After overnight incubation at 37 °C and 5% CO 2 , the cells were incubated with 100 μg/ml PLL-Au-Fe 3 O 4 NPs. After incubation for another 24 h, the medium was carefully removed and cells were washed with PBS for three times and fixed at 4 °C for 1 h using glutaraldehyde (2.5% in PBS). Then the cells were further subjected to a sequence of treatments to obtain sections that were subsequently mounted on copper grids before TEM measurements.

Photothermal treatment of breast cancer cells using PLL-Au-Fe 3 O 4 NPs
using PBS (3×) to remove the unbound NPs and re-incubated in the corresponding cell culture media for 72 h. The cells were exposed to NIR light (808 nm pulse laser of 1 W/ cm 2 with a diameter of 6 mm for 10 min) to induce photothermal damage. The following control samples were used: cell culture medium, cells without any treatment, and the cells treated with PLL-Au-Fe 3 O 4 NPs without any exposure to lasers. After exposure to the NIR light, cells were incubated for an additional 72 h at 37 °C. Cell viability was assessed using CAM and EthD-1 (Invitrogen). To further confirm the in vitro photothermal ablation of breast cancer cells, cytotoxicity following irradiation was also performed using MTT viability assay (Invitrogen

Statistical analysis
Each experiment was carried out with three independent experiments of at least triplicate measurements. The mean differences and standard deviations were evaluated.

Synthesis and characterization of PLL-Au-Fe 3 O 4 NPs
TEM images revealed that Au-Fe 3 O 4 NPs were uniform and averaged ~ 55 ± 8.6 nm in diameter (Fig. 1a).
The thickness of PLL coating on Au-Fe 3 O 4 was estimated to be approximately 9 ± 2.5 nm by analyzing the TEM images (Fig. 1b and c). Additional file 1: Table S1 shows the amount of PLL coating on Au-Fe 3 O 4 . The hydrodynamic diameter of Au-Fe 3 O 4 NPs in water as characterized using DLS showed a wide size distribution of Au-Fe 3 O 4 dispersions with more than one particle populations and a high polydispersity index (PDI) of 0.856 ± 0.07 (Additional file 1: Figure S2a). The differences in size between TEM and DLS techniques could be explained by NP agglomeration and the presence of small aggregates. The PLL coating decreased the PDI of Au-Fe 3 O 4 NPs from 0.856 to 0.539 ± 0.03 (Table 1). The hydrodynamic diameters of NPs after PLL coating eliminated the large and small particle aggregates in water, PBS, RPMI 1640 cell culture medium and PBS containing 10% FBS indicating a better colloidal stability (Additional file 1: Figure S2b). The stability of PLL-Au-Fe 3 O 4 NPs was further proved using a time-resolved video (Additional file 2: Movie S1). As you can see from this video that Au-Fe 3 O 4 NPs without any coating (left-hand side tube in the video) precipitate down quickly in water while PLL-Au-Fe 3 O 4 NPs (right-hand side tube) were stably suspended in the black emulsion. The Au-Fe 3 O 4 NPs possess a negative surface charge of − 7.9 ± 0.8 mV and − 12 ± 7 mV in water and PBS, respectively as determined by zeta potential (Table 1 and Fig. 2a). The zeta potentials of Au-Fe 3 O 4 NPs increased in cell culture medium and PBS with 10% FBS indicating pronounced differences in the particle surface chemistry caused by different solvent compositions. The PLL coated Au-Fe 3 O 4 NPs showed a strong positive charge in water and PBS due to the positive amine groups on the polymer backbone which confirmed the successful grating of PLL polymer on the surface of NPs (Table 1 and Fig. 2b). This further confirms that the PLL coating made the NPs disperse better in aqueous solutions and as a result no agglomeration on storage. Particles that are surface engineered with amine functional groups like PLL has been reported to the effective release of encapsulated molecules from endosomal compartments [37].
The To confirm the successful synthesis of NPs, UV-Vis absorption and FT-IR spectra were measured. A complete spectra analysis of Au-Fe 3 O 4 NPs shows a broad surface plasmon absorption with an absorption maximum at around 710 nm (λ max ) ( Fig. 3b; dotted line) [38]. The PLL coating showed an absorption shift to lower wavelengths with an absorption maximum at 640 nm ( Fig. 3b; solid line). This explains the enhanced dispersion of PLL-Au-Fe 3 O 4 NPs in the aqueous phase by redistributing agglomerated Au-Fe 3 O 4 NPs.
FT-IR spectra were used to study the transformation of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NP compositions (Fig. 3c). As shown in Fig. 3c (Fig. 3d). The PLL coating results in a weight loss of 7.4% between 100 and 650 °C when compared with the uncoated particles (Au-Fe 3 O 4 ). No change in PLL-Au-Fe 3 O 4 mass was observed above 850 °C. Combinedly these findings suggest a successful surface functionalization of Au-Fe 3 O 4 NPs by PLL polymer coating.

Determination of T 2 magnetic relaxation of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs using magnetic relaxometer
It is important to determine the overall magnetic properties of Au-Fe 3 O 4 and PLL-Au-Fe 3 O 4 NPs for cancer imaging by MRI technique. It is expected that the synthesize Fe 3 O 4 nanocomposites will be MR active as they are  Figure S4). Clearly, cells treated with NPs show a remarkable distribution inside endoplasmic vesicles of the cells.

Photothermal effects by PLL-Au-Fe 3 O 4
In order to investigate, the potential of PLL-Au-Fe 3 O 4 as nanothermal ablators, suspensions of the NPs in PBS were irradiated using 808 nm light emitted by a laser. The photothermal behavior of PLL-Au-Fe 3 O 4 NPs was investigated by a temperature change versus the NP concentration (Fig. 5). Clearly, the NPs were able to induce a temperature enhancement in a concentration-dependent manner. The temperature of the NP suspension reached 50 °C at the PLL-Au-Fe 3 O 4 NP concentration of 800 μg/ ml. Laser irradiation of PBS negative control without NPs did not show any temperature increase under the same conditions. The results indicate that the synthesized PLL-Au-Fe 3 O 4 NPs were able to transform NIR laser into heat under laser irradiation. For laser treatment, BT-474 and MDA-MB-231 cells were first incubated with PLL-Au-Fe 3 O 4 NPs for 2 h followed by a wash process to remove un-internalized NPs, laser irradiation for 10 min and then for additional 72 h incubation period. In the control groups (cells + laser irradiation in absence of NPs), no significant cell death was observed. The cells treated with 100 μg/ml of PLL-Au-Fe 3 O 4 NPs but without laser illumination reached 90 ± 4.7% of cell survival rate compared to those treated with PBS control. In contrast, the combination of PLL-Au-Fe 3 O 4 NPs and laser treated cells underwent photothermal destruction as shown by both phase contrast and cell viability (green live cells) and dead cell (red stain) staining (Fig. 6).
The groups for PLL-Au-Fe 3 O 4 NPs + 10 min exposure to laser illumination at 1 W/cm 2 showed the inhibition in cell growth by 49 ± 12% in BT-474 cells ( Fig. 7; filled circle) and 60 ± 10% in MDA-MB-231 cells ( Fig. 7; open circle) suggesting significant therapeutic effects following the photothermal treatment. Cells without any treatment, with laser treatment alone and with NP groups showed ≤ 5% inhibition in cell growth. The cytocompatibility of PLL-Au-Fe 3 O 4 NPs was further assessed by MTT cell viability assay (Additional file 1: Figure S5). The quantitative analysis further reveals that the percentage of cell viability decreased to 63.5 ± 5.5% and 31.6 ± 3.2% in BT-474 and MDA-MB-231 cells, respectively at concentrations ≥ 10 μg/ml of NPs following laser irradiation.

Discussion
A dumbbell-shaped Au-Fe 3 O 4 superparamagnetic NPs is synthesized that is similar in morphology to multifaceted Janus particles [39,40]. The structure (Au-decorated Fe 3 O 4 ) is chosen to provide added advantages of both Au and Fe 3 O 4 functionalities for the full utilization of their potential. Several Au dots on the Fe 3 O 4 host ensures that there is a maximum number of spots for molecular recognition since Au-terminal acts as anchors for targeting agents. Perhaps the most challenging aspect of applying Au-Fe 3 O 4 NPs involves the colloidal stability and shelflife, surface functionalization, cellular internalization, and biocompatibility. Designing a properly grafted surface is therefore of paramount importance. Dextran [41], PEG [42], and silica coating [43] have been used extensively, however, each method has its benefits and drawbacks and requires trade-offs and optimizations. For example, although silica coatings can provide colloidal stability, it may also retard R 2 relaxation in MRI imaging, as well dampen the superparamagnetic moment which reduces hyperthermia efficiency. Reduction in the superparamagnetic moment also leads to the necessity for increased dosage of the magnetic NPs. In that regards, the Januslike particle with larger Fe 3 O 4 anchored with several Au dots serves the multifaceted purpose of retaining high superparamagnetic moment over larger size [35] as well as optimizing SPR and photothermal effect of Au. Here, we report a simple and versatile method to adsorb PLL on bare Au-Fe 3 O 4 dispersed in aqueous solutions. The polycationic PLL backbone ensures tight coulomb attachment onto anionic surfaces of Au endowing the NP surface with a robust coverage. This approach can be generalized to many anionic surfaces onto which cationic polymers can adhere tightly, such as glass or silica. The results are comparable with previous studies on Au nanoshells where polymers (i.e., polyethylene imine; PEI) have been used as an intermediate separating layer during the fabrication of Au-Fe 3 O 4 where the polymer layer prevents the migration of Au shell into the magnetic core by connecting between the core and shell structure [44,45]. In contrast, we show an outer layer of PLL on the surface of Au-Fe 3 O 4 that attribute to the columbic interactions between the Au surface and aliphatic monoamines that is clearly responsible for the observed stability of Au-Fe 3   of PLL of approximately 9 nm thickness. The PLL coating improved the interaction of negatively charged Au-Fe 3 O 4 at the cellular level by the resulting surface charge as confirmed by the zeta potential data. The next step of PLL-Au-Fe 3 O 4 involves cell culture experiments that suggest the overall intracellular uptake of the NPs at a non-toxic dose in breast cancer cells. The live/dead assay indicates that PLL-Au-Fe 3 O 4 NPs are not cytotoxic in breast cancer cells at concentrations ≤ 100 μg/ml (Fig. 5). When compared to other cell viability data of polymer-coated NPs, our results are comparable to the literature data showing 20% reduction in cell viability using similar NP concentrations [45,46]. Furthermore, the results from the phase contrast imaging microscopy demonstrated the effective internalization of the NPs presumably due to the combination of electrostatic interaction with the negatively charged glycocalyx on the cell membrane [47,48] and the receptormediated endocytosis via EGCG [49][50][51][52][53]. The results are in agreement with the previous finding where Au NPs functionalized with methoxy-PEG-thiol were internalized by MDA-MB-231 cells via endocytosis [54,55]. Importantly, the observed uptake of PLL-Au-Fe 3 O 4 NPs by breast cancer cells associated with low toxicity suggest a potential theranostic use of these Au NPs. It is worth noting that PLL-Au-Fe 3 O 4 had higher levels of uptake in MDA-MB-231 cells than BT-474 cells. The differences in cell surface protein expressions and proteoglycans may attribute to the differential uptake of NPs inside the cells [56][57][58]. Importantly, the higher observed uptake of PLL-Au-Fe 3 O 4 in MDA-MB-231 than BT-474 cells was associated with pronounced toxicity (Fig. 5 and  6) suggesting a potential theranostic use of these gold nanoparticles.
Multiple studies have demonstrated the heating effect of Au shell NPs. Thermal ablation using PEG-coated Au nanoshells with silica cores have been reported to induce photothermal morbidity in SK-BR-3 breast cancer cells [59]. The treated cells revealed lost in cell membrane integrity and cell death that was not observed in the controls with laser irradiation or gold nanoshells alone [59]. Photothermal destruction was effective in reducing colon tumors in mice with a mean survival life of 90 days after the treatment [60]. We found that at 100 μg/ml of PLL-Au-Fe 3 O 4 and 10 min laser exposure, a ΔT of 15 ± 7.6 °C was achieved. The current study reveals the effectiveness of using PLL-Au-Fe 3 O 4 as a potent MRI-visible photosensitizer during the laser irradiation of cancer cells [45,61,62]. The noticeable combination of properties of PLL-Au-Fe 3 O 4 with the local application of NIR laser irradiation offers a promising approach for the photothermal ablation therapy of breast cancer cells following internalization inside cells.

Conclusions
A multifunctional NP was constructed using the PLL polymer coating on Au-Fe 3 O 4 with a mean diameter of ~ 60 nm that are less prone to aggregation and thus suitable for a wide range of biological applications. PLL-Au-Fe 3 O 4 NPs showed good colloidal stability, NIR light absorption property, magnetic relaxivity and cytocompatibility. Upon exposure to a NIR light, the SPR of Au increased their temperature inside the cells. The PLL-Au-Fe 3 O 4 NPs were also demonstrated the importance of having a surface of the polymer layer that enhanced MRI contrast. As an integrated all-inone NP platform, the polymeric theranostic agent was shown for intracellular uptake and hyperthermal treatments of breast cancer cells for further translational therapeutic applications.