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DOI: http://dx.doi.org/10.15688/)volsu10.2014.4.7
УДК 620.22:620.1 ББК 30.3
SURFACE-MODIFIED MAGNETIC NANOPARTICLES FOR CELL LABELING
Zasonska Beata A.
PhD, Professor, Institute of Macromolecular Chemistry, Academy of Sciences of the Czech Republic office@imc.cas.cz
Heyrovskeho Sq., 2, 16206 Prague 6, Czech Republic
Patsula Vitaliy
PhD, Professor, Institute of Macromolecular Chemistry, Academy of Sciences of the Czech Republic office@imc.cas.cz
Heyrovskeho Sq., 2, 16206 Prague 6, Czech Republic
Stoika Rostyslav
Doctor of Biological Sciences, Professor,
Head of the Department of Regulation of Cell Proliferation,
Institute of Cell Biology of National Academy of Science of Ukraine
institut@cellbiol.lviv.ua
Drahomanov St., 14/16, 79005 Lviv, Ukraine
Horak Daniel
® PhD, Professor, Institute of Macromolecular Chemistry,
Academy of Sciences of the Czech Republic ¿g office@imc.cas.cz
<3 Heyrovskeho Sq., 2, 16206 Prague 6, Czech Republic DC
pi
Abstract. High potential of the polymer-coated magnetic nanoparticles can be envisioned 2 for many biological applications. The particles can be easily magnetically separated and redispersed in water solutions upon removing of the external magnetic field.
Key words: magnetic nanoparticles, surface-modified, cell labeling, iron oxide, thermal decomposition.
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jg 1. Introduction nanoparticles driven by the rapid development of
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g the nanomedicine and nanobiotechnology [1].
^ A great effort has been recently devoted to Among them, iron oxide nanoparticles, in particular,
© the design and synthesis of new magnetic magnetite Fe3O4 and maghemite Fe2O3, nhich play
a prominent role since iron is indispensable component of living organisms and reduces toxicity [15]. Surface-modified iron oxide nanoparticles have been found very attractive for cell separation [14] and labeling [3], cancer therapy [27], drug delivery [26] and as contrast agents for magnetic resonance imaging (MRI).
There are many methods to obtain various types of iron oxide nanoparticles differing in shape, morphology, size and availability of the reactive groups on the surface.The oldest preparation involves the size reduction [20], i.e. grinding of bulk magnetite in the presence of large amounts of surfactant in a ball mill for 500-1,000 h. Other synthetic approaches for development of magnetic nanomaterials include hydrothermal process [33], sol-gel method [32] or spray pyrolysis [31]. However, the most popular techniques for preparation of such particles include coprecipitation of Fe(III) and Fe(II) salts in the presence of an aqueous base (e.g., NH4OH or NaOH) or thermal decomposition of organo-metalic complexes in high-boiling solvents [12]. For the latter, precursors, such as Fe(III) acetyl acetonate [34], FeN-nitrosophenylhydroxylamine [24] or Fe(CO)5 were suggested [35]
Iron oxide nanoparticles possess a lot of unique properties, such as small size (~100 nm) allowing them to function at the cellular level, super-paramagnetism, high magnetization and large specific surface area. However, neat (uncoated) particles show high nonspecific adsorption of biomolecules,undesirable in vitro and in vivo interactions, relative toxicity and tendency to aggregate [4]. This can be avoided by their surface modification with biocompatible polymers which also determines ability of the nanoparticles to interact with living cells in a well-defined and controlled manner, as well as ensures immunotolerance and biocompatibility.Typical polymer shells are made from organic, like poly(ethylene glycol) (PEG) [9] poly(vinyl alcohol) [10], poly(N,N-dimethyl-acrylamide) (PDMAAm) [5], or inorganic materials, e.g. silica [16]. This additional layer can render the particles with colloidal stability, avoids interactions with the surrounding environment and introduces specific functional groups on the surface.
In this chapter, synthesis, properties and some applications of new poly (N,N-dimethylacrylamide)-coated maghemite (g-Fe2O3@PDMAAm), silica-coated maghemite(g-Fe2O3@SiO2) and methyl-poly(ethyleneglycol)-
coated magnetite (Fe3O4@mPEG) nanoparticles are described. Both PDMAAm and silica are hydrophilic, chemically inert and biocompatibile materials, hence, they are attractive for drug delivery systems and applications in medical diagnostics. Moreover, the polymerscan behave like transfection agents enabling efficient engulfment of the particles by the cells, e.g. stem or neural cells and macrophages. Macrophages, that are formed in response to an infection and accumulate damaged or dead cells, are important in the immune system [19]. These large, specialized cells can recognize, engulf and destroy foreign objects.Through their ability to clear pathogens and instruct other immune cells, they play a pivotal role in protecting the host. They also contribute to the pathogenesis of inflammatory and degenerative diseases [11]. Labeling of macrophages with magnetic particles enables thus their tracing in the organism using magnetic resonance imaging (MRI).
2. Preparation of magnetic nanoparticles
Chemical and physical properties of magnetic nanoparticles, such as size and size distribution, morphology and surface chemistry, strongly depend on selection of the synthetic method, starting components and their concentration [11, 22]. Nanoparticles ranging in size from 1 to 100 nm exhibit superparamagnetic behavior. In this report, two methods of iron oxide synthesis are presented.
Coprecipitation method. Typical synthesis of magnetic nanoparticles is exemplified by formation of maghemite (g-Fe2O3) during coprecipitation of Fe(II) and Fe(III) salts followed by oxidation of Fe3O4 with sodium hypochlorite [23]. Briefly, 0.2 Maqueousiron(III) chloride (100ml) and 0.5 M iron(II) chloride (50 ml) were sonicated for a few minutes and mixed with 0.5 Maqueous ammonium hydroxide (100 ml). The mixture was then continuously stirred (200 rpm) at room temperature for 1 hour. Formed Fe3O4 nanoparticles were magnetically separated and seven times washed with distilled water. Subsequently, the colloid was sonicated with 5 wt.% sodium hypochlorite solution (16 ml) and again five times washed with water to obtain the final g-Fe2O3 nanoparticles.
Thermal decomposition. Another possibility to produce superparamagnetic nanoparticles consists in thermal decomposition of iron organic compounds, e. g. iron(III)
oleate [24]. The method allows preparation of monodisperse Fe3O4 nanoparticles with controlled size. As an example, we describe preparation of iron(III) oleate by reaction of FeCl3 • 6H2O (10.8 g) and sodium oleate (36.5 g) in a water/ ethanol/hexane mixture (60/80/140 ml) at 70 °C for 4 h under vigorous stirring. The upper organic layer was then separated, three times washed with water (30 ml each) and the volume reduced on a rotary evaporator. Obtained brown waxy product was vacuum-dried under phosphorus pentoxide for 6 h. The resulting Fe(III) oleate (7.2 g) and oleic acid (4.5 g) were then dissolved in octadec-1-ene (50 ml) and heated at 320 °C for 30 min under stirring (200 rpm). The reaction mixture was cooled to room temperature, the particles precipitated by addition of ethanol (100 ml) and collected by a magnet. Obtained nanoparticles were then five times washed with ethanol (50 ml) and redispersed in toluene and stored.
3. Modification of the nanoparticle surface
Disadvantage of neat iron oxide colloids is that they induce undesirable interactions, e.g. adhesion to the cells. To prevent this, it is recommended to coat the iron oxide surface with a biocompatible polymer shell. Surface of the g-Fe2O3 nanoparticles was therefore firstly modified with an initiator and V,V-dimethylacrylamide was then polymerized from the surface. 2,2'-azobis(2-methylpropionamidine) dihydrochloride (AMPA) served a suitable polymerization initiator. In contrast, if the particles were hydrophobic, i.e. obtained from the thermal decomposition, they
were dispersible only in organic solvents. To make them water-dispersible and suitable for biomedical applications, their surface was modified with mPEG derivatives via a ligand exchange.
3.1.Coating with poly (N, N) -dimethylacrylamide (PDMAAm).
Coating of the g-Fe2O3 nanoparticles with PDMAAm via grafting from approach is schematically shown in Figure 1. In the following, example of this synthetic approach is described in details. The polymerization was run in a 30-ml glass reactor equipped with an anchor-type stirrer. First, the AMPA initiator (4.8 mg) was added to 10 ml of the colloid (47 mg g-Fe2O3/ml) during 5 min, DMAAm (0.3 g) was dissolved and the mixture purged with nitrogen for 10 min. The polymerization was started by heating at 70 °C for 16 h under stirring (400 rpm). After completion of the polymerization, the resulting g-Fe2O3@PDMAAm particles were magnetically separated and washed ten times with distillated water until all reaction byproducts were removed. Advantage of the g-Fe2O3@PDMAAm particles consists in possibility to introduce additional functional comonomer into the shell to attach a highly specific bioligand, such as antibody, peptide or drug.
3.2. Coating with tetramethoxyortosilicate (TMOS) and (3-aminopropyl)triethoxysilane (APTES).
Another frequently used coating of iron oxide particles is based on silica. Silica is generally synthesized by hydrolysis and condensation of tetraethylorthosilicate (TEOS) or tetramethyl-orthosilicate (TMOS) (Figure 2). Neat silica particles are obtained by Stober method in ethanol under
Fig. 1. Scheme of preparation g-Fe2O3@PDMAAm nanoparticles via grafting from approach using 2,2'-azobis(2-methylpropionamidine) dihydrochloride (AMPA) initiator
Г-он NH'0H ; ^^ -o-Loh , ^^-o-I
TMOS, HP ^F I APTES IF I
I ?
Fig. 2. Scheme of silanization of g-Fe2O3 with tetramethylorthosilicate (TMOS) and modification of g-Fe2O3@SiO2 nanoparticles with (3-aminopropyl)triethoxysilane (APTES)
the presence of ammonia catalyst [25] or in surfactant-stabilized reverse microemulsion containing two phases [26]. The g-Fe2O3 nanoparticles were coated by a silica shell using TMOS according to earlier published method [27]. Shortly, solution containing 2-propanol (24 ml), water (6 ml) and 25 wt.% aqueous ammonia (1.5 ml) was mixed with g-Fe2O3 colloid (1 ml; 50 mg g-Fe2O3) for 5 min. TMOS (0.2 ml) was added and the mixture stirred (400 rpm) at 50 °C for 16 h. Resulting g-Fe2O3@SiO2colloid (Figure 3, c, g) was then five times washed with ethanol using magnetic separation. In the next step, amino groups were introduced on the particle surface using (3-aminopropyl)triethoxysilane(APTES). In a typical experiment,g-Fe2O3@SiO2 nanoparticles were dispersed in ethanol (50 ml) under sonication for 15 min and APTES (0.15 ml), ethanol (20 ml) and water (1 ml) were added. After completion of the reaction, the resulting g-Fe2O3@SiO2-NH2 particles (Figure 3, d, h) were washed with water.
3.3. Coating with methyl-poly(ethylene glycol) (mPEG).
In order to make the hydrophobic iron oxide particles dispersible in water, their surface was modified by a ligand exchange method [28]. As a hydrophilic ligand, mPEG was selected due to its non-toxicity, hydrophilicity and low opsonization in biological media. mPEG was terminated with groups, such as phosphonic (PO(OH)2) [29] and hydroxamic (NHOH) acid [30], exhibiting strong interactions with the iron ions. Fe3O4 particles prepared by thermal decomposition were coated by mPEG terminated with phosphonic (PA-mPEG) or hydroxamic acid (HA-mPEG). In the following, the surface modification is described in a more detail. HA- or PA-mPEG (70 mg) and hydrophobic Fe3O4 nanoparticles (10 mg) were added to 4 ml of tetrachloromethane/toluene mixture (1:1 v/v) and sonicated for 5 min. The mixture was then heated at 70 °C for 48 h under vigorous stirring. The Fe3O4@PEGnanoparticles were purified by repeated precipitation with petroleum ether (3 x 30 ml) at 0 °C and diethyl ether (3 x 30 ml) and redispersed in water.
4. Properties of the surface-modified iron oxide nanoparticles
The synthesized surface-modified iron oxide particles were thoroughly characterized by a range
of methods including transmission (TEM) and scanning electron microscopy (SEM), atomic absorption spectroscopy (AAS), attenuated total reflectance Fourier transform infrared spectroscopy (ATR FTIR), dynamic light scattering (DLS) and magnetic measurements. Shape of the iron oxide particles prepared by the coprecipitation and thermal decomposition methods was spherical and cubic, respectively. The number-average diameter (Dn) of the g-Fe2O3 particles prepared by precipitation was 1 0 nm (TEM) and polydispersity index PDI (DJDn) = 1.24 (Dw is the weight-average diameter) suggesting a moderately broad particle size distribution (Figure 3, a). Since it was rather difficult to control size and particle size distribution by the precipitation method, thermal decomposition approach was investigated. Size of the Fe3O4 particles was controlled in the 8-25 nm range and monodispersity was achieved (Figure 4). For example, if the reaction temperature increased from 320 to 340 °C, the D increased from 8 nm
' n
(Figure 4, a) to 17 nm (Figure 4, b) due to an increase in the growth rate of the nanoparticles. If the concentration of oleic acid stabilizer increased from 0.008 to 0.08 mmol/ml, the particle size decreased from 12 to 8 nm (Figure 5) because more particles are stabilized. However, the particles prepared by this method were hydrophobic; the organic shell formed ~ 80 wt.% of the total mass according to AAS. Such particles formed very stable colloids in organic solvents, such as toluene or hexane, but not in water. Magnetic properties of the nanoparticles were described earlier [22].
Compared with the neat nanoparticles, Dn of the dried g-Fe2O3@PDMAAm nanoparticles was larger (12 nm) due to presence of the shell, but the polydispersity substantially did not change (PDI 1.18; Figure 3, b).The hydrodynamic diameter Dh of g-Fe2O3@PDMAAm, PA - and HA-mPEG-coated Fe3O4 was substantially larger, i.e. 206, 35 and 68 nm, respectively, than Dn.
The reason consists in that the DLS provided information about Dh of the particle dimers and clusters in water, where hydrophilic PDMAAm chains swell. Zeta potential (ZP) of the g-Fe2O3@PDMAAm, PA- and HA-mPEG-Fe3O4 was -53, 26.3 and 12.4 mV, respectively. Since ZP of the g-Fe2O3@PDMAAm was highly negative, the nanoparticle dispersions were very stable (up to a few months) due to the electrostatic repulsion.
g
h
Fig. 3. (a-d) TEM and (e-h) SEM micrographs of (a, e) neat superparamagnetic g-Fe2O3 nanoparticles synthesized by coprecipitation method, (b, f) g-Fe2O3@PDMAAm (via grafting from approach), (с, g) g-Fe2O3@SiO2 and (d, h) g-Fe2O3@SiO2-NH2 nanoparticles
Regardless of the low positive ZP of the Fe3O4@mPEG particles, their colloid solutions were also very stable due to steric repulsion provided by mPEG. PA-mPEG-Fe3O4 colloid (Dh~40 nm) was stable also at various NaCl concentrations ranging from 1 to 1000 mmol/l. In contrast, HA-mPEG-coated Fe3O4 (Dh~65 nm) demonstrated stability only at 1 and 10 mmol of NaCl/l.ATR FTIR and Fe analysis confirmed successful coating of the iron oxide nanoparticles with both PDMAAm by the grafting method and mPEG by ligand exchange method [22; 36].
Optionally, the g-Fe2O3 nanoparticles were covered with a silica shell at various g-Fe2O3/TMOS ratios (0.1-0.8 w/w) to control the morphology and size of the nanoparticles observed by TEM (Figure 3, c) and SEM (Figure 3, g). Size of the g-Fe2O3@SiO2 particles ranged from 12 to 192 nm depending on the g-Fe2O3/SiO2 ratio (Figure 6). With increasing amounts of silica relative to the iron oxide and with introduction of amino groups by reaction with APTES, Dn of the g-Fe2O3@SiO2 and g-Fe2O3@SiO2-NH2 nanoparticles increased (Figure 3, d) due to their aggregation. This was accompanied with broadening of the particle size distribution. According to AAS, content of iron decreased from 66.1 in g-Fe2O3 to 27.7 and 19.8 wt.% in g-Fe2O3@SiO2 and g-Fe2O3@SiO2-NH2 nanoparticles, respectively. This was inagreement with increasing thickness of the silica shell surrounding the g-Fe2O3 particles. Nevertheless, this amount of iron was sufficient to confer the particles with good magnetic properties. Coating of the g-Fe2O3 particles with a thin silica shell hindered particles from aggregation and made them hydrophilic; as a result, the particles were well dispersible in water. Secondary coating obtained by reaction of g-Fe2O3@SiO2 particles with APTES made possible prospective attachment of a target biomolecule, e.g. protein, antibody, enzyme or drug. However, g-Fe2O3@SiO2-NH2 nanoparticles often formed aggregates at neutral pH suggesting that the initial g-Fe2O3@SiO2 particles agglomerated during the reaction with APTES.
5. Engulfment of the nanoparticles by stem cells and macrophages
Labeling of the cells with surface-functionalized iron oxide nanoparticles is increasingly important for diagnostics and
separation of DNA [25], viruses [32], proteins [33] and other biomolecules [34]. A great deal of attention is recently devoted to stem cells and their ability to differentiate in any specialized cell type. Earlier, we have developed poly(L-lysine)-coated g-Fe2O3 nanoparticles (g-Fe2O3@PLL) and g-Fe2O3@PDMAAm particles obtained by the solution radical polymerization in the presence of g-Fe2O3 [5]. Such particles were found to be highly efficient for in vitro labeling of human (hMSCs) and rat bone marrow mesenchymal stem cells (rMSCs). In this report, both g-Fe2O3@PDMAAm obtained by grafting approach and g-Fe2O3@SiO2 nanoparticles were investigated in terms of their engulfment by macrophages (Figure 7). This is an important task from the point of view of controlling introduction, movement and overall fate of the labeled cells after their implantation in the organism.
In a typical stem cell labeling experiment, the hMSCs or rMSCs were cultured in Dulbecco's Modified Eagle's Medium (DMEM) in a humidified 5 % CO2 incubator; the medium was replaced every 3 days until the cells grew to convergence. Uncoated, g-Fe2O3@PLL, g-Fe2O3@PDMAAm particles (via the solution polymerization) and the commercial contrast agent Endorem® (dextran-coated iron oxide) were then used for labeling the stem cells. After 72 h of labeling, the contrast agent was stained to produce Fe(III) ferrocyanide (Prussian Blue). The quantification of labeled and unlabeled cells was performed using TEM and inverted light microscope. Compared with Endorem® and unmodified nanoparticles, the PDMAAm- and PLL-modified particles demonstrated high efficiency of intracellular uptake into the human cells. Optionally, the labeled rMSCs cells were intracerebrally injected into the rat brain and magnetic resonance (MR) images were obtained. MR images of the g-Fe2O3@PDMAAm (via the solution polymerization) and g-Fe2O3@PLL-labeled rMSCs implanted in a rat brain confirmed their better resolution compared with Endorem®-labeled cells [18; 35].
In our experiments, both g-Fe2O3@PDMAAm (via grafting approach), g-Fe2O3@SiO2 and g-Fe2O3@SiO2-NH2 nanoparticles (4.4 mg/ml) were opsonized with FBS proteins at 37 °C for 24 h. They were then incubated with murine J774.2 macrophages and stained with Acridine Orange and
Hoechst 33342. Uptake of the particles by the cells and their morphological changes were analyzed using fluorescence microscopy. Cytotoxicity of the g-Fe2O3@PDMAAm and neat g-Fe2O3 nanoparticles was estimated using a hemocytometric chamber for counting number of the cells treated in the presence of nanoparticles (0.025, 0.5 and 1 wt.%) in the culture medium for 24 h.
The efficiency of the engulfment of the g-Fe2O3@ PDMAAmand neat g-Fe2O3 nanoparticles by the murine J774.2 macrophages was determined after 30 min, 1, 2, 3 and 24 h cell cultivation in the presence of the particles. Figure 7 shows Acridine Orange and Hoechst 33342-stained macrophages treated with the nanoparticles for 3 h. After 30-min treatment of J774.2 macrophages with g-Fe2O3@PDMAAm nanoparticles, their majority remained unengulfed in the culture medium. Visible engulfment of the nanoparticles appeared after 1-h treatment. After 2-h treatment, granulation of the cytoplasm was observed due to accumulation of the
g-Fe2O3@PDMAAm nanoparticles in the peripheral region of the cytoplasm. After 3-h treatment, majority of the g-Fe2O3@PDMAAm nanoparticles was engulfed by the macrophages and some cells demonstrated signs of lysosomal activation characterized by red Acridin Orange fluorescence. Only a minimal amount of the g-Fe2O3@PDMAAm nanoparticles remained unengulfed indicating that the engulfment was very efficient. PDMAAm showed the affinity to cell membrane components facilitating thus the endocytosis.
As a control experiment, the engulfment of the neat g-Fe2O3 nanoparticles in the macrophages was investigated. Within 1-3 h treatment, the number of vacuoles, their size, as well as the number of lysosomal clusters associated with large vacuoles, increased with time. Numerous unengulfed g-Fe2O3 nanoparticles were accumulated on the surface of treated macrophages, while free g-Fe2O3 nanoparticles were almost absent. The size of the cells treated with g-Fe2O3 nanoparticles was also increased.
a b
Fig. 4. TEM micrographs of (a) 8 and (b) 17 nm superparamagnetic Fe3O4 nanoparticles prepared by thermal decomposition method at (a) 320 and (b) 340 °C
Oleic acid (mmol/ml)
Fig. 5. Dependence of number-average diameter Dn of Fe3O4 nanoparticles on oleic acid concentration. Particles were prepared in octadec-1-ene at 320 °C for 30 min
All described superparamagnetic nanoparticles were relatively non-toxic for the cultured cells. Apparently, for the efficient particle engulfment by the macrophages, the presence of positively charged amidine groups in g-Fe2O3@PDMAAm nanoparticles is beneficial. The efficiency of engulfment of the g-Fe2O3@PDMAAm nanoparticles was quite high since after 2-h treatment most cells engulfed the nanoparticles and only few nanoparticles remained in the culture medium. Fluorescence microscopy confirmed only weak activation of lysosomes, which manifested itself by a change in the color of
Acridine Orange from green to red. Acridine Orange, a weakly basic amino dye, is known to be a lysosomotropic agent. In its stacked form, i.e. in lysosomes, it emits red fluorescence, while in the cell nuclei at neutral pH it emits yellow-green fluorescence. Activation of macrophages during the engulfment of foreign extracellular materials was accompanied by an increase in the activity of digestive vacuoles and, thus, it caused a red fluorescence shift due to accumulation of the dye in lysosomes. Activation of lysosomal compartments accompanied intracellular processing of the engulfed particles
200 -
0
0.0 0.2 0.4 0.6 0.8 1.0
y-Fe2O3/SiO2 (w/w)
Fig. 6. Dependence of number-average diameter Dn of g-Fe2O3@SiO2 particles on g-Fe2O3/SiO2 ratio
c d
Fig. 7. Fluorescence micrographs of murine J774.2 macrophages treated with (a) g-Fe2O3, (b) g-Fe2O3@PDMAAm (via grafting approach), (c) g-Fe2O3@SiO2 and (d) g-Fe2O3@SiO2-NH2 nanoparticles
(microorganisms, viruses, damaged cells, and foreign macromolecules) [36]. Chemical structure of uncoated g-Fe2O3 nanoparticles thus provided potential toxicity for the treated cells, which manifested itself by time-dependent evolution of vacuoles in the cell cytosol.
6. Conclusions
In summary, two different types of iron oxide nanoparticles were synthesized, maghemite (g-Fe2O3) and magnetite (Fe3O4). The first ones were prepared by coprecipitation of Fe(II) and Fe(III) salts with aqueous ammonia. Obtained magnetite was then oxidized with sodium hypochlorite to chemically stable maghemite. However, the size distribution of these particles was rather broad as determined by a range of physico-chemical characterization methods including SEM, TEM and DLS measurements. In contrast, monodisperse superparamagnetic Fe3O4 nanoparticles with size controlled from 8 to 25 nm were produced by the thermal decomposition of Fe(III) oleate at different temperatures and oleic acid concentrations. The particles were successfully transferred in water by the ligand exchange method. As a hydrophilic ligand, derivatives of mPEG with specific functional groups were used that strongly chemically bonded with iron. Optionally, g-Fe2O3 particles were surface-modified with PLL, PDMAAm (both by the solution radical polymerization and grafting from method) or SiO2. The successful coating of the iron oxide nanoparticle surface was confirmed by both ATR FTIR spectroscopy and Fe analysis. The colloidal particles were stable in aqueous media for several months.
The biotargeting characteristics of the nanoparticles are mainly defined by the biomolecules conjugated to the particle surface.It is desirable that the particle shell contains either membranotropic molecules like phospholipids, poly(ethylene glycol) or macromolecules (proteins) present in biological fluids. In this work, surface of the formed nanoparticles was opsonized with proteins available in the fetal bovine blood serum. The g-Fe2O3@PDMAAm and g-Fe2O3@SiO2 nanoparticles, in contrast to the neat nanoparticles were shown to be non-cytotoxic and intensively phagocytozed by the mammalian macrophages. Additionally, there was no cell irritation during the phagocytosis of the g-Fe2O3@PDMAAm
nanoparticles. In contrast, time-dependent vacuolization of neat g-Fe2O3 nanoparticles in cytoplasm of the macrophages was observed suggesting cytotoxicity of the material.
Silica used as an inorganic inert coating of the g-Fe2O3 nanoparticles proved to be also suitable modification agent preventing aggregation of the particles and enhancing their chemical stability. This inorganic material is also easily susceptible to chemical modifications which make synthesis of particles for combined diagnosis and therapy possible. Biological experiments demonstrated that both g-Fe2O3@PDMAAm and g-Fe2O3@SiO2 and g-Fe2O3@SiO2-NH2 core-shell nanoparticles were recognized and engulfed by the macrophages. The uptake of the surface-coated iron oxide nanoparticles by phagocytic monocytes and macrophages could provide a valuable in vivo tool by which magnetic resonance imaging can monitor introduction, trace movement and observe short- and long-term fate of the cells in the organism.
In conclusion, high potential of the polymer-coated magnetic nanoparticles can be envisioned for many biological applications. The particles can be easily magnetically separated and redispersed in water solutions upon removing of the external magnetic field. Magnetically labeled cells can be steered and concentrated inside the body by a magnet. The iron oxide particles, modified with organic, as well as inorganic polymer coatings, seem to be very promising not only for cell imaging and tracking, but also for drug and gene delivery systems and capture of various cells and biomolecules required for diagnostics of cancer, infectious diseases and neurodegenerative disorders.
Acknowledgement. The financial support of the Ministry of Education, Youth and Sports (project LH14318) is gratefully acknowledged.
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ПОВЕРХНОСТНОЕ МОДИФИЦИРОВАНИЕ МАГНИТНЫХ НАНОЧАСТИЦ ДЛЯ СОТОВЫХ МАРКЕРОВ
Засонска Беата А.
PhD, профессор института макромолекулярной химии, Академия наук Чешской Республики office@imc.cas.cz
Площадь Гейровского, 2, 16206 г. Прага 6, Чехия
Патсула Виталий
PhD, профессор института макромолекулярной химии, Академия наук Чешской Республики office@imc.cas.cz
Площадь Гейровского, 2, 16206 г. Прага 6, Чехия
Стойка Ростислав
Доктор биологических наук, профессор,
руководитель Департамента регулирования клеточной пролиферации,
Институт биологии клетки НАН Украины
institut@cellbiol.lviv.ua
ул. Драгоманова, 14/16, 79005 г. Львов, Украина
Горак Даниэль
PhD, профессор института макромолекулярной химии, Академия наук Чешской Республики office@imc.cas.cz
Площадь Гейровского, 2, 16206 г. Прага 6, Чехия
Аннотация. Магнитные наночастицы с полимерным покрытием могут быть использованы для многих биологических приложений. Частицы легко отделить с помощью магнитного поля и обнаружить в водных растворах после снятия внешнего магнитного поля.
Ключевые слова: магнитные наночастицы, поверхностно-модифицированный, сотовые маркеры, оксид железа, термическое разложение.
