DOI: 10.24075/brsmu.2018.080


Lipidoid iron oxide nanoparticles are a platform for nucleic acid delivery to the liver

About authors

1 Laboratory of Biomedical Nanomaterials, National University of Science and Technology MISiS, Moscow

2 Center of Life Science, Skolkovo Institute of Science and Technology, Moscow

3 Laboratory of Tissue Specific Ligands Investigation, Lomonosov Moscow State University, Moscow

4 Department of Physical Materials Science, National University of Science and Technology MISiS, Moscow

5 Mendeleev University of Chemical Technology of Russia, Moscow

Correspondence should be addressed: Victoria I. Uvarova
Leninsky 4, Moscow, 119049; ur.kb@ayirotkiv_avoravu

About paper

Funding: the study was funded by the Ministry of Science and Higher Education of the Russian Federation. Project 14.578.21.0201 (ID RFMEFI57816X0201).

Received: 2018-06-26 Accepted: 2018-08-25 Published online: 2018-12-30

The term “hyperlipidemia” describes abnormally elevated levels of low-density lipoproteins and their metabolites in blood serum. Hyperlipidemia is a significant contributing factor in the risk of atherosclerosis and cardiovascular disorders [1], which, in turn, are a leading cause of death worldwide [2]. One of the approaches to treating this pathological condition is the silencing of genes responsible for elevated lipoproteins levels in plasma. [3, 4]. For example, lipoprotein levels can be lowered by inhibiting the synthesis of proteins participating in lipoprotein metabolism, such as angiopoietin-like protein 3 or apolipoproteins B and C3 produced by liver hepatocytes [5]. The major obstacles to safe and effective gene therapy aimed at reducing lipoprotein levels arise from the difficulties that complicate targeted delivery of antisense therapeutic agents to hepatocytes and the release of therapeutic agents from endocytic vesicles [6, 7].

Platforms for the delivery of antisense drugs are traditionally classified into viral and nonviral [8, 9]. Viruses effectively transport foreign genetic material to cells. However, intense debate is continuing about the safety of viral carriers: adenoviral vectors can induce a strong immune response and their retroviral counterparts pose a risk of insertional mutagenesis [10]. Nonviral delivery systems comprise vectors based on inorganic nanoparticles (NP) [11], liposomes [12, 13], and complexes with cationic lipids or polymers [14, 15].

Lipidoids are lipid-like materials holding great promise for effective targeted drug delivery. They can be used both as drug carriers and NP surface coatings for the subsequent loading of nucleic acids. RNA delivery systems based on the C12–200 lipidoid exhibit high efficacy in laboratory animals, including rodents and nonhuman primates [16]. Lipid nanoparticles need auxiliary components for better performance. Those include fusogenic phospholipids (DSPC), which improve transfection efficacy of the system by destabilizing the lipid bilayer of cell membranes, PEG lipids (mPEG2000-DMG), which reduce immune response by stabilizing LNP and protecting them from macrophages, and cholesterol, which fills the space between the lipid molecules on the NP surface and enhances the activity of cationic lipids [17].

Transfection methods vary greatly in their efficacy determined by the accuracy of drug delivery to a target cell, interactions between the carrier and the cell membrane and the release of the carrier from endosomes. Once endocytosed, nonviral vectors can get trapped by the endosomal compartment of the cell, suffering subsequent degradation of the therapeutic gene they carry [18]. New strategies are being sought to facilitate release of viral vectors from endosomes, which will naturally improve the efficacy of transfection.

Magnetic iron oxide NP offer a solution to the problem of poor transfection efficacy of nonviral vectors. Magnetite and maghemite nanoparticles have a few attractive properties beneficial for such biomedical applications as targeted drug delivery, magnetic hyperthermia, and contrast-enhanced MRI [19]. Importantly, magnetic NP can be used to attain controlled drug release in biological objects, including cells and experimental animals, made possible by the effect of Brownian relaxation, which in essence is intense oscillations of magnetic particles induced by a low-frequency magnetic field. This approach can significantly improve the efficacy of therapeutic agents: some researchers report that magnetic liposomes (liposomes enriched with magnetic NP) demonstrate better performance in the targeted delivery of doxorubicin and paclitaxel than their conventional counterparts [20, 21].

The functional properties of drug delivery systems based on magnetic NP are largely determined by their magnetic properties. For example, their suitability as contrast agents is influenced by their size and geometry [22].

In this study we attempted to design a platform for targeted delivery of antisense nucleic acids based on iron oxide nanocubes functionalized with a lipid formulation and to test the obtained carrier for the efficacy of drug delivery into hepatocytes in vivo.


The following reagents were used: 1-octadecene, trioctylamine, dibenzyl ether, oleic acid, sodium oleate, iron oleate (III), anhydrous sodium acetate, cholesterol, 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC), 1,2-dimyristoyl-sn-glycero- 3-methoxypolyethylene glycol monomethyl ether (DMG-mPEG), N-methyl-2-pyrrolidone (Sigma-Aldrich; USA), hydrochloric acid, nitric acid, ethanol, butanol-1, chloroform (SigmaTec; Russia), 1,1’-(2-(4-(2-((2-(bis(2-hydroxydodecyl)amino)ethyl) (2-hydroxydodecyl)amino)ethyl)piperazine-1-yl) ethylazanediyl) didodecane-2-ol (C12-200), DMEM and DMEM/F12, deionized water.

Cell cultures

The initial stock of Huh7 cells was provided by the Department of RNA Structure and Functions of A.N.Belozersky Research Institute of Physico-Chemical Biology. HepG2 cells were purchased from a cell bank (ATCC, HB-8065). Manipulations with the cells were carried out in the SafeFAST Elite 212 S sterile class II microbiological safety cabinet (Faster; Italy). The cells were cultured in the MCO-18AIC CO2 Incubator (Sanyo; Japan) at 37 °C in 5% СO2 environment. The culture medium for Huh7 cells was DMEM (Corning, catalog number 10-013- CV) supplemented with 4.5 g/l glucose, 10% fetal bovine serum and 4 mM L-glutamine. HepG2 cells were cultured in DMEM/ F12 (Gibco™, catalog number 21331020) containing 10% fetal bovine serum and 4 mM L-glutamine.

Animal model

The experiments were carried out in adult female BALB/c mice (age of 6–7 weeks, weight of 19–20 g) purchased from the Central breeding nursery of the Academy of Medical Sciences (Andreevka; Russia) and kept in individually ventilated cages. The study was approved by the Ethics Committee of Pirogov Russian National Research Medical University (Protocol 1/2016 dated February 3, 2016).

Synthesis of lipidoid nanocubes

Precursor iron (III) oleate was synthesized following a protocol described in [23]. Magnetite nanocubes with an average size of 16 nm (CbS) were obtained through thermal decomposition of the precursor in a high-boiling organic solvent. The detailed description of the procedure is available in [24].
Nanocubes with an average size of 27 nm (CbB) were synthesized in two steps. In the first step, magnetic nuclei (seeds) were obtained as described above. In the second step, the precursor was introduced into the reaction mixture to stimulate NP growth. Briefly, 37.5 mg of the seeds, 0.35 g of sodium oleate and 0.32 g of oleic acid were loaded into a three-neck flask equipped with a mercury thermometer. Then, a solvent mix was added consisting of 2.85 g trioctylamine and 3.13 g of dibenzyl ether. The resulting mixture was heated to 110 °С under vigorous stirring under argon flow and maintained under such conditions for 1 h. After that, the mixture was heated to a boiling temperature at a rate of 5 °С/min. Subsequently, 20 ml of 0.2 М iron (III) oleate solution in dibenzyl ether were added dropwise to the mixture at 3 ml/h, which was then left to boil for 20 min and cooled down to room temperature. The synthesized NP were separated from the reaction mixture by magnetic decantation in the presence of butanol-1. The precipitate was redispersed in chloroform and sonicated for 5-10 min.
The nanoparticles were coated with a lipidoid formulation using the phase transfer approach [25]. The coating consisted of the С12–200 lipidoid [26], cholesterol, DSPC and DMG-mPEG taken at a mass ratio of 75 : 15 : 7 : 3. The mass percent of the lipid formulation used to coat CbB and CbS was 0.9 and 1% (relative to magnetite), respectively.

Characterization of physical and chemical properties of the obtained nanoparticles

Transmission electron microscopy (TEM)

The obtained nanoparticles were imaged under the JEOL 1200- EX II transmission electron microscope (JEOL; Japan) operating at an accelerating voltage of 100 kV. Samples for TEM were prepared by applying 1–2 μl of the NP solution onto a formvar-coated copper mesh (d = 3.05 mm) that was subsequently left to air-dry. Further manipulations with images necessary to determine the distribution of NP sizes and characterize NP morphology was done in ImageJ ver. 1.50d (Wayne Rasband (NIH); USA).

X-ray diffraction analysis (XRD)

The crystalline structure of the particles was studied by X-ray diffraction on the DRON-4 diffractometer (Burevestnik; Russia) with the following settings: CoKα radiation with λ = 0.179 nm, tube voltage of 40 kV, and current of 30 mA. The samples were scanned through a range of diffraction angles 2θ from 20° to 120° by increments of 0.1°. Exposure time was 3 seconds per frame. Phases were identified by comparing the obtained data to the database of about 200,000 X-ray spectra in PHAN software.

Thermal gravimetric analysis and differential scanning calorimetry (TGA/DSC)

TGA and DSC were performed using the simultaneous thermal analyzer Netzsch STA 449 F3 (NETZSCH; Germany). The samples were placed into alundum crucibles and heated in the temperature range from 50 to 800 °С at 10 °С/min under argon flow. Before the analysis, solvents were removed from the samples by evaporation using a rotary evaporator.

Vibrating-sample magnetometry

Static magnetic properties of the nanoparticles were profiled by applying a range of magnetic fields from –20 to 20 kOe at 300 K. Measurements were done using the Quantum Design Physical Property Measurement System (PPMS; Germany) equipped with a vibrating sample magnetometer with an oscillation amplitude of 2 mm and frequency of 40 Hz. The sensitivity of the system was 10-6 emu.

Photon correlation spectroscopy (PCS)

The hydrodynamic sizes and ζ-potential (charge) of the particles coated with a lipid formulation were measured by PCS in 0.5 mg/ml LNP solutions in phosphate-buffered saline (1×PBS) or distilled water. The solutions were poured into plastic or glass cuvettes. The analysis was carried out at 25 °C using Zetasizer Nano ZS (Malvern; Germany). The ζ-potential of the particles was measured in distilled water using disposable capillary cuvettes for ζ-potential measurements.

Cytotoxicity of lipidoid nanoparticles in vitro

LNP cytotoxicity was assessed by the МТS-assay (3-(4,5-dimethylthiazol-2-yl)-5-(3-carboxymethoxyphenyl)-2- (4-sulfophenyl)-2H-tetrazolium) [27]. Human hepatocellular carcinoma cells (Huh7 and HepG2) were seeded onto 96- well plates at 5,000 cells per well and cultured at 37 °С in 5% СO2 environment until 70% confluence of the monolayer was achieved, which took 48 hours. Then, СbS and CbB were introduced into the wells at magnetite concentrations of 370, 187, 94, 47, 23, 12, and 6 μg/ml and 420, 210, 105, 52, 26, 13, and 6 μg/ml, respectively. After that, the cells were incubated at 37 °С in 5% СO2 for 24 h and washed. Then, the MTS reagent was added to the wells. Cells incubated in a culture medium supplemented with equivalent volumes of phosphate buffered saline (1×PBS) were used for control. Optical density was measured using the plate reader VictorX3 (PerkinElmer; USA) at λ = 490 nm. The proportion of the survived cells was calculated as a ratio of optical density of cells treated with nanoparticles to the optical density of untreated controls. Graphs were constructed and IC50 (half-maximal inhibitory concentration) was calculated in GraphPad Prism 8.0.0 (GraphPad Software; USA).

Study of biodistribution of nanoparticles

Biodistribution of LNP was studied in BALB/c mice divided into 3 groups of 3. The animals from the experimental group received 120 μl of the LNP solution (an iron concentration of 720 μg/ml) intravenously. The control group did not receive any injections.

Studying the dynamics of LNP accumulation by MRI

The animals were scanned by the 7Т animal MRI scanner ClinScan (Bruker Biospin; USA). Transverse T2-weighted images were obtained in the fat-suppression mode with the following Turbo Spin Echo (TSE) parameters: TR/TE = 2000/42 ms, slice thickness = 1 mm, matrix = 380 x 640, FOV = 34 x 60 mm.
To assess the dynamics of NP accumulation, scans were performed before the LNP injection and 1, 12, 24, and 48 hours after it.

Histological examination

Forty-eight hours after the LNP injection, the animals were euthanized with a lethal dose of Zoletil® injected intraperitoneally. After the reflexes were gone, the abdominal cavity was opened by a midline incision. The rib cage was cut laterally on both sides, perpendicular to the rib bones. The right atrium was dissected and perfused with 40 ml of PBS. The solution was supplied through a needle introduced into the left ventricle and attached to a Janet’s syringe via a cannula. Then the cervical vertebrae were dislocated and the organs were excised, including the liver, spleen, kidneys, and lungs. The removed organs were submerged in 4% paraformaldehyde and stored at 4 °С until further analysis. Sixty-μm-thick slices were prepared using the Thermo Scientific Microm HM 650 V Vibration system (Thermo Fisher Scientific; USA) and Perls-stained using the Iron Stain Kit (Sigma-Aldrich; USA). Perls staining involves treating histological slices with a mixture of hydrochloric acid and potassium hexacyanoferrate (II). The reaction between the mixture and the deposits of iron compounds in a histological slice produces a Prussian blue pigment. Its granules of different shades of blue can be seen under a light microscope. The samples were washed in distilled water twice, incubated in 70% glycerol and imaged under a light microscope by Carl Zeiss (Germany) equipped with Axioplan 2 Imaging camera.

Biodistribution of iron in the internal organs of mice assessed by inductively coupled plasma atomic emission spectroscopy (AES)

Paraformaldehyde-fixed organ fragments (one-third of the liver and spleen, one kidney, one lung and a half of the heart) were dissolved in 2 ml of a freshly prepared mix consisting of 1,500 μl of concentrated hydrochloric acid (HCl) and 500 μl of nitric acid (HNO3). The fragments were incubated in the acid mix for 24 h. Then, water was added to bring the volume of the dissolved liver and spleen to 20 ml and of the heart, kidney and lung, to 10 ml. After the calibration curve was constructed, iron concentrations were measured in the obtained solutions using the 4200 MP–AES machine (Agilent Technologies; USA).


TEM images of monodisperse nanocubes with an average size of 16 nm (CbS) and histograms of their size distribution are presented in fig. 1A. TEM images of bigger nanocubes (CbB) sized 20–30 nm show that CbB samples have distinct morphology and a well-faceted cubic shape (fig. 1B).

X-ray diffraction analysis yielded very similar results for both CbS and CbB samples: the positions of diffraction peaks in the diffraction pattern correspond to the inverse spinel structure of magnetite with lattice constants of 0.838 nm and 0.839 nm for CbS and CbB, respectively (fig. 2A). Hysteresis loops (fig. 2B) indicate that CbS and CbB are ferrimagnetic materials with coercivity of 20–30 kA/m. Magnetic saturation (Ms) of CbS is 61 А • m2/kg. Large nanocubes (CbB) have Ms of 89 А • m2/kg. In our study, magnetic saturation was normalized to the amount of the iron oxide phase (minus the mass of organic stabilizers) determined by TGA/DSC (fig. 2C).

The TG curve constructed for CbS has three regions indicating abrupt weight loss: the first recorded at 150–300 °C corresponds to the desorption of organic compounds noncovalently bound to the surface of NP; the second recorded at 300–450 °C corresponds to the desorption of covalently bound stabilizers; the third recorded over a temperature range of 600–700 °С occurs when magnetite undergoes phase transition. The region of the CbB TG curve showing desorption of covalently and noncovalently bound organic molecules looks smoother; phase transition is observed at temperatures over 500 °C.

Nanocubes with hydrophobic residues of oleic acid on their surface can be dispersed in nonpolar organic solvents (chloroform, hexane) and can be regarded as a colloid system resistant to sedimentation. The average hydrodynamic size of CbS and CbB in chloroform is shown in fig. 3A. The polydispersity index (PdI) is 0.113 and 0.151 for NP with an actual average sample of 16 and 27 nm, respectively. To stimulate the phase transfer of magnetite NP to an aqueous phase, the particles were coated with a lipid formulation consisting of the lipidoid С12-200, cholesterol, DSPC, and 1,2-DMG-mPEG taken at a mass ratio of 75 : 15 : 7 : 3. The average hydrodynamic size of the coated CbS in the aqueous phase increased to 50.9 nm (PdI = 0.119) (fig. 3B). Based on the size distribution pattern, we inferred that the majority of CbS nanocubes were present in the solution as individual particles, while the minority tended to aggregate into clusters. The pattern of CbB size distribution was completely opposite: the average hydrodynamic size of CbB particles was 118.6 nm (PdI = 0.201) (fig. 3B), which is 4 times bigger than their actual size, suggesting more vigorous aggregation of nanocubes functionalized with lipids. The value of the ζ-potential of magnetite-based LNP in water was positive and equaled +20.5 mV and +34.3 mV for CbB and CbS, respectively.

The survival of HepG2 and Huh7 cells incubated with CbS and CbB is shown in fig. 4. Using the MTS assay, we calculated IC50 for CbB: it was 21.5 μkg/ml (magnetite concentration) for HepG2 and 126 μkg/ml, which is 6 times higher, for Huh7. CbS did not exhibit any cytotoxic activity at studied concentrations.

fig. 5A features representative T2-weighted coronal images that clearly show that the most pronounced NP accumulation could be observed in the liver and spleen of the experimental mice 0–48 h after the intravenous injection of the formulation. The accumulation of both CbS and CbB was noticeable as early as 1 hour after the injection and its level remained stable for the next 48 hours. This suggests that intravenously injected NP are readily taken up by the liver and spleen. It should be born in mind, though, that MRI is a semi-quantitative modality and cannot be used to conclusively distinguish between the accumulation patterns of different NP types in different organs. Therefore, we additionally employed AES to study iron accumulation in the internal organs of the experimental mice (fig. 5B). AES revealed that LNP tended to be sequestered mostly by the liver and spleen, which was consistent with MRI findings (fig. 5A). LNP deposition in other organs was negligible. The CbS sample accumulated in the liver most effectively: the liver retained 84% of the injected LNP amount, whereas CbB showed poor accumulation in this organ (only 43% of the injected LNP amount).

The images of Perls-stained liver slices clearly demonstrate that both types of iron-based NP increasingly build up in the liver in comparison with the controls (fig. 6). There was a difference in the pattern of iron accumulation between the CbS and CbB samples. CbS diffusely spread in the liver parenchyma (presumably, depositing in hepatocytes), whereas CbB exhibited a mixed discoloration pattern: some of the particles deposited in irregular-shaped cells (presumably, macrophages) lying at the border between the sinusoids and the parenchyma, and some produced diffuse discoloration evident of their buildup in hepatocytes.


The classic process of NP growth can be broken down into 3 stages: in the first stage, the precursor — iron (III) oleate — decomposes producing unstable iron-organic intermediates until their critical concentration is reached necessary for nucleation. In the second stage, the concentration of the intermediates declines as these molecules attach to the surface of magnetic seeds stimulating their growth. In the last stage, the concentration of the intermediates drops to thermodynamically stable levels, and the generated NP undergo Ostwald ripening. A steady rate of NP growth can be maintained by the controlled addition of a precursor, making NP expand in size while retaining their monodispersity. Using this approach, one can synthesize NP with a programmed size (as large as required) characterized by low polydispersity, which is particularly important for the particles with dimensions over 20 nm. When added to the reaction mixture, a stabilizer (potassium oleate) that can be specifically adsorbed onto the plane (111) promotes formation of cube-shaped nanoparticles (fig. 1B). In our study, the rate at which the precursor was supplied to the mixture in the second stage of synthesis, its concentration and duration of its addition were determined experimentally. At low rates, NP underwent Ostwald ripening: the mass was transferred from small particles to large, promoting polydispersity. At high rates, the concentration of intermediates in the reaction mixture surged triggering the mechanism of primary nucleation and increasing NP polydispersity.

For both samples, the results of the conducted X-ray diffraction analysis are consistent with the literature [28].
For CbS, magnetic saturation (Ms) agrees with the values reported for average-sized magnetite NP comparable in their dimensions with CbS particles [:lit_23, 29;]. The Ms of large cube-shaped NP (CbB) was very high and comparable to that of a massive sample [30] or huge NP [31].

According to the results of the TGA/DSC analysis (fig. 2C), the amount of the organic phase adsorbed onto the surface of iron oxide NP constitutes 15.5% of the total CbS and 11.7% of the total CbB masses. For samples with similar masses, an increase in the average size of NP entails an increase in the ratio of their surface area to their volume. The process yields more stabilizing molecules that can be adsorbed onto the NP surface. This significantly affects the stability of the studied colloidal system largely determined by 2 factors: steric stabilization ensured by the presence of long hydrophobic residues of oleic acid adsorbed onto the surface of NP and the aggregation of those residues caused by mutual magnetism. As the magnetic core grows, the PdI of the CbB sample increases (as demonstrated by PCS) and the peak of its hydrodynamic size broadens, as compared to CbS, suggesting more vigorous clusterization of the particles resulting from the magnetic core growth, which, in turn, is caused by intense magnetic interactions.

The hydrodynamic size of NP and the physical and chemical properties of their surface largely determine the pattern of intercellular interactions, endocytic routes and the efficacy of NP uptake by the cell [32, 33]. The internalization of NP into cells causes disorganization of the cytoskeleton [34, 35]. When accumulated in abundance, NP induce disruption of the actin and microtubule networks in neural progenitor cells of mice and primary endothelial cells of human blood vessels [36]. We hypothesized that the mere physical presence of sufficient amounts of NP captured by large lysosomal structures normally found near the nucleus sterically impairs the function of the cytoskeleton and causes reorganization of the actin network. The results of cytotoxicity tests correlate well with a hypothesis that establishes a link between the disruption of the cytoskeleton and NP toxicity: the studied concentrations of the CbB sample, whose actual size was 1.7 bigger than that of CbS, were toxic against the used cell lines, unlike CbS, whose phase composition, coating and morphology were similar.

The initial characteristics of magnetic NP, including size and shape homogeneity, resistance to aggregation, and stability of the coating, are key to the pharmacokinetics and biodistribution of the particles. It is well known that NP with the hydrodynamic size of less than 20–30 nm are filtered by renal glomeruli and those over 200 nm in size build up in the liver [37]. Nanoparticles with the dimensions between 30 and 200 nm are normally sequestered in the liver: they can be easily captured by endocytic vesicles with an average diameter of 40-60 nm. However, particles over 150 nm in size (the upper limit for entering the cell through caveolae) are engulfed by macrophages. Therefore, an ideal hydrodynamic LNP size to be taken up by the liver would be 30 to 150 nm. The histological examination and the analysis of NP biodistribution in the organs of mice reveal that the CbB particles are mainly accumulated in the reticuloendothelial system, which explains the even distribution of NP between the liver and spleen. These findings correlate well with other studies [38]. In contrast, the CbS sample is not sequestered in macrophages but is caught by hepatocytes instead, leading to its buildup in the liver. This fact is consistent with the literature describing the behavior of NP with a magnetic core of a comparable size [39]. Perhaps, larger nanocubes (CbB) grow in size when introduced into the bloodstream of a mouse because they adsorb serum proteins on the surface which form a crown of biomolecules [40], thereby increasing the hydrodynamic size of NP; as a result, the latter accumulate in the spleen.


The proposed platform for the delivery of antisense drugs into liver hepatocytes has proved to be effective both in vivo and in vitro. The synthesized CbS lipid-coated nanoparticles exhibit low toxicity against Huh7 and HepG2 cell lines. The analysis of in vivo biodistribution of differently sized LNP with magnetic cores reveals significant accumulation of the particles in the liver as early as 1 hour after the injection. The level of accumulation remained stable for 48 hours following the injection. Nanocubes with magnetic iron oxide cores sized 10 to 20 nm and a hydrodynamic size of <100 nm increasingly accumulated in hepatocytes (>80% of the injected dose) whereas larger NP were readily taken up by Kupffer cells and other components of the reticuloendothelial system.