Strategies to enhance nanoparticle-endothelial interactions under flow

1 Introduction

Nanoparticles represent a versatile platform, adjustable for therapy and diagnostics of various human diseases. Although multiple delivery routes are possible, the majority of the clinically-relevant nanocarriers, such as anti-cancer and anti-inflammatory nano-drugs, are expected to require intravascular administration. For this purpose, a rational design of drug carriers is necessary to limit their cyto- and genotoxicity, prevent their clearance by reticuloendothelial system (RES) thus increasing the circulation half-life of their cargo, and to deliver a sufficient payload of therapeutics to the diseased regions. Ongoing efforts address these key issues in nanoparticle development, as the previous generations of injectable nanocarriers have often been plagued by suboptimal efficacy, as a result of rapid clearance by the RES [1], or an overall inability to reach the designated target in effective dosage [2–4].

Among the materials most commonly used for the synthesis of intravascular drug delivery systems are the nanoparticles or nanoshells made of natural or synthetic polymers, such as liposomes, dextrans, poly(lactic-co-glycolic acid) (PLGA), polyaccrylates, as well as metal or metal oxide nanoparticles (e.g. gold, silver, superparamagnetic iron oxide nanoparticles (SPIONs)), and quantum dots. Several of the commonly reported drug-carrier systems (reviewed in detail in [5]) are briefly outlined below.

Liposomes are composed of a lipid bilayer consisting of amphipathic phospholipids (primarily phosphatidylcholine) that enclose an interior aqueous space [6]. Being synthesized from naturally occurring phospholipids, liposomes have relatively low toxicity [6, 7], but are easily cleared from the circulation by RES. The stability and circulation time of liposomal formulations can be greatly improved by conjugation of the head groups of phospholipids with polymerizable moieties (e.g. polyethylene glycol (PEG)). Liposomes are often functionalized with maleimide, which allows conjugation of antibodies or other targeting ligands [8]. Among their advantages as a drug delivery platform are the ease of preparation, commercial availability and overall low immunogenicity [9], which is expected to enable safe and repeated administration. However, the effects of shear forces on the liposomal bilayer integrity are largely unknown. Thus far, a PEGylated liposomal formulation of doxorubicin (Doxil^®) has been the first FDA-approved nanodrug indicated for the treatment of several types of cancer, including AIDS-related Kaposi’s sarcoma, recurrent ovarian cancer, metastatic breast cancer and multiple myeloma (reviewed in [10]).

PLGA is the most common biodegradable polymer approved for use in humans, frequently used in form of nanoshells or nanocarriers. The favourable safety profile of PLGA results from its physiological degradation to easily metabolized products, namely lactic acid and glycolic acid [11]. In animal models, PLGA nanoparticles have been tested as drug carriers for tissue plasminogen activator (mouse model of thrombosis [12]), pitavastatin (rat model of myocardial ischemia-reperfusion [13]), superoxide dismutase (mouse model of stroke [14]), as well as carriers of several anti-cancer agents [11, 15].

Gold nanoparticles consisting of a dielectric core of silica coated with a metallic layer of gold, are tunable to various sizes and forms [16] and can be used for e.g. for optical imaging, or photothermal ablation therapy, as well as biosensors, or drug carriers. Gold nanoparticles have been utilized for experimental delivery of anti-cancer agents [17–19] and for delivery of inotropic agent (levosimendan) in a rat model of heart failure [20]. However, the important concern related to gold particles is their potential cytotoxicity and a slow elimination resulting in a long-term persistence within many organ systems.

SPIONs consist of iron oxide core, often coated with organic materials such as fatty acids, polysaccharides, or polymers [21, 22]. The magnetic properties of SPIONs allow the remote control of their accumulation by means of external magnetic field [23], as well as their application for hyperthermia-therapy of cancer [24]. However, in contrast to their broad utility as imaging agents [25–29], relatively few reports addressed the use of SPIONs for vascular drug delivery thus far [30, 31].

Notably, the above-described materials can be freely combined in order to achieve the desired characteristics of the nanoparticles, e.g. biocompatibility or contrast enhancement. Such hybrid nanosystems with adjustable characteristics are expected to improve the future clinical utility and safety of nanotherapies. Still, the successful development of novel intravascular nanosystems for disease-specific imaging and drug delivery requires extensive studies in vitro and in vivo. Apart from considering the disease mechanisms and pathological processes, these novel therapeutic approaches would greatly benefit also from the knowledge of endothelial biology and endothelial transport mechanisms to ensure adequate safety and effective drug delivery, thus increasing therapeutic success of intravascular nanosystems.

2 Endothelial functions in health and disease

In the mammalian body, the circulating blood is separated from the surrounding tissues by a biological barrier consisting of endothelial cell monolayer. The endothelium, an expansive cell monolayer covering a total surface area of 4000–7000 m² in an average-sized human [32], is a highly metabolically active organ. Apart from fulfilling the barrier function, endothelial cells are involved in many physiological processes, including the control of vasomotor tone, leukocyte adhesion and trafficking, thrombocyte adhesion and hemostasis. In response to inflammation and injury, endothelial barrier function in microvessels is reduced: Increased capillary permeability allows the migration of immune cells into the diseased or injured tissues, in order to protect the tissues from harmful pathogens, damaged cells or irritants [33]. In the medium and large arteries, however, increased vascular permeability may play a deleterious role, contributing to the formation of atherosclerotic plaques, which are initiated by the subendothelial accumulation of blood lipids and inflammatory cells.

Oxygen and nutrients supply is maintained in almost all tissue types by a vast network of blood capillaries distributed not further apart than the diffusion limit of oxygen, which is 200 μm [34]. In tumours, wounds, or atherosclerotic plaques alike, hypoxia is thus a driving stimulus for angiogenesis. Without blood vessels, the neo-plasms and neo-tissues cannot grow beyond a critical size.

In physiological angiogenesis, increased microvessel permeability and matrix degradation are followed by endothelial cell migration and proliferation [35, 36]. The resulting thin-walled, permeable sprouts undergo a tightly-regulated maturation process, involving the basement membrane formation and pericyte recruitment. Sprouting from the pre-existing vessels is also the main route for tumor angiogenesis which, however, lacks the coordinated temporal and spatial regulation, leading to structural and functional abnormalities and vessel immaturity. In contrast to normal vascular network, tumour vessels are tortuous and unevenly dilated, with excessive branches and shunts [35]. These vessels are also leaky with numerous endothelial fenestrae, vesicles and transcellular holes and widened intercellular junctions. The basement membrane is discontinuous or absent, and the mural cells are missing. Similar observations have been reported for atherosclerotic plaque neovasculature, where intraplaque microvascular endothelial cells showed numerous abnormalities, such as membrane blebs, intracytoplasmic vacuoles, open intercellular junctions, and basement membrane detachment [37]. This compromised structural integrity of the intraplaque microvessels can lead to enhanced leukocyte infiltration, leakage and hemorrhage [38, 39].

In terms of the therapeutic approaches, the immaturity of the tumor or plaque neovessels improves the chances of efficient drug delivery [36]. For example, without a microvascular network, the delivery of anti-cancer drugs in effective quantities to the center of the tumour would not be possible. Moreover, the capillary leakage improves the possibility of drug accumulation in the tumor, as the compromised endothelial barrier results in leaky vessels with intercellular gap sizes of 100 nm to 2 μm depending on the tumor type [40–42]. Additionally, tumors lack a proper lymphatic drainage system, which results in an increased interstitial pressure at the center of tumors relative of the tumor periphery [43]. Therefore, drugs and nanoparticles that cross blood-tumor tissue barrier have higher retention times than in normal tissues. This combination of leaky vasculature and poor lymphatic drainage results in so-called Enhanced Permeation and Retention (EPR) effect [44], so that the nanoparticles which enter the interstitium via immature vessels can be entrapped in the tumor [43, 45].

3 Intravascular drug delivery strategies

In order to design safe carriers, thorough preclinical analyses of the candidate nanosystems intended for intravascular administration are necessary, including their basic physicochemical characterization and the biological effects of nanoparticles on the vascular cells and blood components. Furthermore, it is important to consider the effects of hemodynamic forces on nanoparticle behaviour in circulation and adhesion to the endothelium.

To date, two main strategies are proposed to deliver nanocarriers to the vascular wall, including passive and active targeting. The former approach exploits the enhanced permeability of the endothelium, particularly in inflammatory diseases and cancer, where the extravasation of nano-sized particles is facilitated [44]. Nanoparticles that prolong the circulation half-life of the carried drugs are therefore expected to increase the payload of drugs reaching the target site. Passive targeting can also utilize nanoparticle properties, in particular cationic charge [46], to increase non-specific cell targeting of negatively-charged endothelial glycocalyx [47–50]. However, despite the presence of leaky vessels in tumors and the compromised blood-brain barrier in many brain disorders, the efficacy of drugs and passively-targeted drug carriers applied via intravenous route is often insufficient for a meaningful clinical improvement. In parallel, increasing the systemic dose in attempt of achieving the sufficient drug efficacy is often impossible due to numerous adverse effects. For this reason, nanoparticulate carriers that can be functionalized for actively-targeted drug delivery [8] constitute an attractive alternative for therapy of e.g. cancer or neurodegenerative diseases [18].

The active targeting of nanoparticles to vascular wall is achieved by grafting the surface or the shell of the nanocarriers with specific ligands or antibodies to molecules expressed on the endothelium. This targeting approach has been shown to allow a better control of nanoparticle biodistribution and to enhance their therapeutic efficacy (see below). Depending on the disease context, various endothelium-expressed molecules have been tested as targets for nanoparticles, including vascular endothelial growth factor receptors [51, 52] and integrins [53, 54] in cancer (reviewed in [44]) as well as adhesion molecules in inflammation and atherosclerosis (reviewed in [55]), as also discussed in a dedicated chapter below.

Another promising strategy of drug delivery, which results in increased drug payloads in the target tissue, at the same time reducing their systemic dose and toxicity, is based on so-called “magnetic drug targeting”. In this approach, conjugation of superparamagnetic particles with drugs, in combination with an external magnetic field is used to target the nanoparticles to the diseased vasculature regions as demonstrated by the studies in a rabbit model of cancer [56–58], a mouse model of thrombosis [59], a mouse model of cardiac ischemia [60] and several mouse models of cancer [61–63].

4 Regulation of endothelial function and nanoparticle interactions by the flow patterns

The specific hemodynamic conditions characteristic of the target vasculature region are expected to modulate the particle internalization and therapeutic efficacy. The wall shear stress in humans varies between 0.5–6 dyn/cm² in the veins, 3–7 dyn/cm² in the peripheral arteries (e.g. the brachial or femoral artery), and 10–15 dyn/cm² in the central arteries (e.g. the carotid artery) [64]. In terms of nanocarrier-mediated drug delivery to microvasculature (e.g. pulmonary circulation), the hemodynamic forces may be of lesser relevance, as the single file flow in microvessels and capillaries [65] increases the contacts of nanoparticles with the vessel wall. However, the interactions and binding dynamics of drug carriers targeted to the endothelium in medium and large-diameter arteries may, apart from inflammatory status [66], largely depend also on local hemodynamics and blood rheology that govern both the endothelial responsiveness and the behavior of blood-borne cells and particles, as briefly discussed below.

In the arteries, the signaling pathways activated by laminar shear stress (including ion channels,G proteins, growth factor receptors, tyrosine kinase receptors, integrins, caveolae, and the cytoskeleton components (reviewed in [67, 68], see Fig. 1), exert a profound anti-apoptotic effect on endothelial cells [69–71], and prevent cytokine-induced expression of pro-inflammatory genes and endothelial adhesion molecules [72–74]. Moreover, endothelial glycocalyx thickness strongly depends on the shear stress patterns. Laminar shear stress promotes glycocalyx formation in ECs [75–77] and thick and negatively charged endothelial glycocalyx improves the barrier function [78, 79]. In contrast, the exposure to disturbed, non-uniform shear stress renders endothelial cells prone to inflammatory activation, and increases the permeability of monolayer to immune cells and blood components [74, 80–82]. Additionally, upon exposure to non-uniform shear stress, the glycocalyx becomes stiffer and loses its buffering function [75–77], thus further increasing the endothelial permeability [83]. Therefore, shear stress-activated intracellular processes may represent the major modulators of the nanoparticleinternalization by arterial endothelial cells. Moreover, due to the larger size of the vessels, the rheological behavior of blood cells in the arterial flow differs from that in the microvessels [84–86]. Erythrocyte accumulation in the center of the lumen and the formation of rouleaux, leaving a cell-free layer at the vessel wall, may strongly affect the margination of nano-sized particles [87].

5 Nanoparticle internalization under flow conditions

Although endothelial cells represent the first-contact cells for nanoparticles administered via intravascular route and are often the key target for therapeutic nanocarriers, relatively few studies have investigated nanoparticle-endothelial interactions under flow conditions, which is a pre-requisite to estimate the cellular responses in physiological-like settings. In terms of nanoparticle applicability in certain diseases (e.g. atherosclerosis), this can critically affect the efficacy of the drug delivery systems or contrast agents accumulation in the diseased regions in vivo. The majority of the existing studies, however, utilize static cell culture conditions to assess the endothelial toxicity of nanoformulations and their cellular interactions. Below, several recent attempts to investigate the influence of shear stress on the uptake of circulating nanoparticles and their effects on endothelial cells in vitro and in vivo are discussed.

From the existing reports, it is clear that the effects of shear stress on the particle uptake is to a large degree dependent on the particle type and the experimental settings, including the selected shear stress magnitude and the exposure time. Samuel et al. [88] compared the short-term effects of shear stress (0, 0.5, 1, and 5 dyn/cm²) on the interactions of negatively charged, thioglycolic acid-coated 2.7 nm and 4.7 nm CdTe quantum dots (QD) and 50 nm silica nanoparticles (NP50) with HUVECs using a microfluidic platform (channel dimensions: 600 μm width×120 μm height×20 mm length). Cell monolayers were exposed to 3 μM negatively charged QD2.7 (2.7 nm), QD4.7 (4.7 nm), or NP50 (50 nm) suspended in PBS for 20 minutes. NP50 did not enter the cytoplasm of cells grown either in static or flow conditions, but were bound to the cell membranes under flow conditions. In contrast, QDs did not show internalization within 20 min under static conditions, but penetrated the endothelial cell cytoplasm and localized near the nucleus under flow conditions [88]. The maximal uptake of QDs was observed at 0.5 dyn/cm², with a decrease at 5 dyn/cm², and was associated with shear stress-induced cytoskeleton reorganization and formation of membrane ruffles, as described for the acute endothelial response to shear stress exposure [89–91]. The cytotoxicity studies carried in static conditions, however, stand in a contradiction with the data on QD4.7 particle uptake: Whereas no uptake was observed within the first 20 min, a significant reduction of in the number of treated cells was detected, indicating a significant toxicity [88], which is unlikely to occur in the absence of particle internalization. Regretfully, neither the consequences of the exposure to QDs under flow conditions on cell viability, nor the effects of prolonged exposure under flow on particle internalization and their cytotoxicity were reported. However, the presented results of long-term static exposure indicate, that although QD are not taken up within the first 20 min of exposure, they must be internalized by endothelial cells also in static conditions upon prolonged incubation: Whereas NP50 did not cause any cytotoxic effect on cultured HUVECs even after 24 h of exposure, a significant reduction in the number of treated cells was observed at all time points (i.e, 0.3, 4, 8, and 24 h) after the QD4.7 treatment. QD2.7 were well tolerated for up to 4 h, followed by a significant decrease in the number of cells at 8 and 24 h, indicating a slower kinetics of particle internalization [88]. Furthermore, it must be noted, that the presented data were obtained on not fully confluent cells, which may affect both the cell behavior and interactions with nanoparticles.

A different approach in vitro was applied by Rinkenauer et al. [92], who utilized a chip-based dynamic cell culture model to pre-expose endothelial cells to different levels of shear stress prior to the incubation with nanoparticles. This model was compared with the static cell culture and a mouse model, in order to assess its capability to predict the in vivo responses to the methacrylate-based nanoparticles. Three types of polymeric nanoparticles of similar size were compared: Negatively charged poly((methyl methacrylate)-co-(methacrylic acid)) with 3% methacrylic acid (3% PMAA, 196 nm, –43.3 mV), poly((methyl methacrylate)-co-(methacrylic acid)) with 13% methacrylic acid (13% PMAA, 205 nm, –38.3 mV), and poly((methyl methacrylate)-co-(2-dimethylamino ethyl-methacrylate)) with 20% 2-dimethylamino ethyl-methacrylate (20% PDMAEMA, 207 nm, +31.3 mV), representing polymers with pH-dependent anionic and cationic charges [92]. HUVECs seeded in rhombic chamber chips (120 μL chamber volume) were exposed to shear stress for 24 h, followed by 60 min perfusion with nanoparticles at a concentration of 200 μg/mL. Shear stress values of 0.7, 3.0, 6.0 and 10.0 dyn/cm² were selected, representing basal nutrient exchange flow with minimal mechanical stimulation observed e.g., in liver sinusoidal vessels (0.7 dyn/cm²) and the shear stress values observed in human circulation. Different effects of shear stress on particle internalization were observed, whereby the low-charged particles (3% PMAA) showed the minimal uptake, with no major differences between static versus flow conditions. A slight increase in the amount of internalized nanoparticles was observed in cells exposed to 10.0 dyn/cm², but it was not statistically significant [92]. The dynamic cell culture at shear stresses of 3 dyn/cm² and higher enhanced the uptake of 13% PMAA particles in a shear stress-dependent manner. Interestingly however, whereas under static conditions 20% PDMAEMA showed the highest uptake, the internalization of these cationic particles was decreased under flow conditions, without a clear shear-stress dependent pattern. In vivo, all tested nanoparticles were mainly cleared by Kupffer cells in the liver, but they were also internalized by the liver-specific endothelial cells to a lesser extent. Similar to the in vitro results, the estimated uptake of 3% PMAA was markedly lower that other particle types, whereas the uptake of 13% PMAA was somewhat lower than 20% PDMAEMA [92].

In a recent study, Fede et al. [93] compared the effects of gold nanoparticles stabilized with sodium citrate on human umbilical vein endothelial cells cultured in static conditions versus cells grown a single-channel microfluidic device (length 4 cm, width 2 mm and height 150 μm) and continuously perfused with nanoparticle suspensions. The authors utilized laminar flow at 30 μL/min, corresponding to about 0.5 dyn/cm² and at 5 μL/min (0.1 dyn/cm²). Despite these relatively low shear stress values, significant differences were observed in gold nanoparticle accumulation after 24 h exposure in cells grown under flow versus static conditions. Under shear stress of 0.1 dyn/cm², the number of nanoparticles per cell was lower by an order of magnitude than in static conditions (2.6×10⁵versus 2.9×10⁶ nanoparticles per cell, respectively). Consequently, the viability of HUVECs exposed to gold nanoparticles in static conditions was significantly reduced at concentrations higher than 5×10¹⁰ nanoparticles/mL (gold concentration 1.6×10^–3 mg/mL), whereas under flow conditions (0.1 dyn/cm²), the fraction of viable cells was approximately 20% higher at 5×10¹¹ nanoparticles/mL, and 1×10¹² nanoparticles/mL [93].

Similar results were obtained in our recent studies utilizing the bifurcating flow channels to compare the nanoparticle toxicity on endothelial cells exposed to laminar shear stress (10 dyn/cm²) or non-uniform shear stress (spatial range 0.6–5 dyn/cm²) [94]. The HUVEC monolayers were perfused for 18 h with medium containing 100 or 400 μg/mL of different types of nanoparticles, including two types of liposomes, lipid nanoparticles of 3 different sizes, 2 types of polyaccrylate particles and 2 types of iron oxide nanoparticles. Both the liposomes and the dextran T6-coated iron oxide nanoparticles showed excellent biocompatibility at static and flow conditions. All lipid nanoparticles, as well as iron oxide nanoparticles coated with lauric acid and albumin, reduced endothelial viability at about 100 μg/mL in static conditions. In contrast, these particles were well tolerated by the cells exposed to flow up to 400 μg/mL, and did not affect endothelial cell morphology, nor induced cell detachment due to shear stress exposure. In the case of poly(isobutylcyanoacrylate) nanoparticles coated with 90% carboxymethyl-dextran and 10% fucoidan, cytotoxic effect was induced from the concentration of 50 μg/mL in static conditions. However, these nanoparticles at 100 μg/mL did not dramatically affect endothelial viability under flow, the cytotoxic effect being observed in the laminar and non-uniform shear stress region at very high concentrations (400 μg/mL). Only for one nanoparticle type (poly(isobutylcyanoacrylate) nanoparticles coated with 80% dextran T70, 10% diethylaminoethyl-dextran and 10% fucoidan), the concentrations affecting cell growth and viability in static conditions (100 μg/mL) also induced cell death under flow conditions [94]. This may be related to the fact that these particles are positively-charged, relatively large (245 nm) and characterized furthermore by a tendency to aggregate. These features may contribute to an increased endothelial uptake even under high shear stress conditions, negatively affecting endothelial viability at concentrations of 100 μg/mL and higher. Collectively, our data indicated that in case of many types of nanoparticles, the longer-term cell culture assays under static conditions may overestimate the potential toxicity. This results from the inherent property of nanoparticles, namely their sedimentation, which occurs over time and leads to increased effective concentrations of nanoparticles in the nearest vicinity of cell monolayer. As shown in our studies, this effect was responsible for the majority, but not all, of the cytostatic and cytotoxic effects observed after 24 h incubation below the concentrations of 200 μg/mL [94].

Regarding the existing reports, it is acutely clear that no meaningful comparisons of the obtained results are possible, as each group utilizes different flow models with differing shear stress magnitudes and durations. To be able to draw conclusions about the effect of physiologic shear stress on nanoparticle internalization, comprehensive standardised studies are necessary that would compare the effects of a broad range of shear stress levels (low vs high), patterns (uniform vs non-uniform) and duration (acute vs chronic) on the particle uptake by endothelial cells in these conditions.

6 Whole blood models

Prior work demonstrated that platelets accumulate within the cell free layer near the vessel walls [95, 96], and that the near-wall concentration of platelet-sized latex beads (2.38 μm diameter) in flowing blood suspensions can be even 3-fold greater than in the central region of the flow [97]. Mathematical studies reported by Lee et al. suggested that compared with spherical particles, elongated particles exhibit larger propensity to laterally drift and marginate in laminar flow and that ellipsoidal micrometer-sized particles display stronger hydrodynamic margination under flow than sub-micrometer andnanometer particles [98]. From this model, the minimum equivalent radii for observing margination under normal hemodynamic conditions (i.e. shear rate of 10³/s) with no external forces would be 7 μm for silica, 3.5 μm for iron oxide and 2 μm for gold particles. Considering silica particles of 500 nm diameter, the modelled contributions of the inertial and gravitational forces under physiological conditions are negligibly small, preventing their margination. This effect is even more valid for lighter particles, such as polymeric or lipid-based beads. The model predicts that under pathological conditions, e.g. within the tumor microcirculation, the gravitational force may dominate leading to the sedimentation of larger particles in horizontal capillaries [98]. These mathematical predictions indicate that, in the absence of external forces, sub-micrometer and nanometer particles of any shape within the circulation can only oscillate around their trajectory. The above-discussed findings were to a large extent confirmed by a series of comprehensive ex vivo investigations concerning the endothelial interactions with nano- and microparticles suspended in human whole blood, reported by the group of Eniola-Adefeso [99, 100]. These authors utilized spherical particles conjugated with sialyl Lewis^a (sLe^a), a ligand specific to the endothelial-expressed selectins, with diameters ranging from 100 nm to 10 μm, showing that nanoparticles (100–500 nm) displayed minimal margination from human blood flowing in chambers of varying heights (125–700 mm) towards endothelial monolayer. In contrast, a significantly higher binding of intermediately-sized microspheres (2–5 μm) was detected in this model [99]. Notably, although microparticle attachment to the endothelium was 2 to 4-fold increased under pulsatile blood flow compared to laminar flow, the margination of nanoparticles was not enhanced. In a further study [100], the authors investigated in detail the effects of geometrical parameters (volume, aspect ratio, axis length) on the margination efficacy of spherical and ellipsoid particles, showing that although margination of rod-shaped microparticles with high aspect ratios was significantly improved as compared to spheres of equal volume, the nanorods did not display enhanced margination compared to that of nanospheres [100]. The authors concluded that both nanorods and nanospheres show no margination in the presence of erythrocytes in vitro, confirming the theoretical predictions of Lee et al. [98]. Thus far, however, the detailed studies which would verify these findings in animal models are missing, and the nanoparticle behavior under flow is expected to differ in dependence of inherent particle properties (size, shape, density, or stiffness) as well as blood rheological parameters, including shear rate, hematocrit, and erythrocyte aggregability [101]. Extensive in vivo investigations at all physiological ranges of shear stress and vessel diameter are thus urgently needed to characterize the ability of particles with different physicochemical properties to deliver drugs to the specific vascular beds.

7 Strategies to enhance endothelial interactions with nanoparticles

The above-discussed in vitro and ex vivo results indicate that many types of nanocarriers may not be adequate for vascular applications in medium and large human arteries due to their small size and/or insufficient margination from the bloodstream. Extensive efforts are therefore focused on identifying efficient targeting approaches that could enhance the binding of nanoparticles to vascular endothelium at the disease-specific regions, including medium and large vessels.

8 Conclusions and perspectives

Nanotechnology-based strategies are expected to have a great clinical impact on the diagnostics and therapy of human diseases in the future. To ensure the clinical safety and feasibility of these entirely novel approaches, a rational design of nanoparticulate contrast agents and drug carriers is necessary. Ideally, the parenterally-administered particles should be able to achieve an increased circulation half-life and a high margination rate, and allow enhanced interactions with endothelial cells in the target region. Passive targeting can be used to deliver nanotherapeutics to the diseased regions, but its efficacy is limited to the vascular beds where the blood-tissue barrier is compromised. In arterial circulation, shear stress-activated processes may significantly affect the nanoparticle internalization by endothelial cells. Therefore, several targeting strategies are employed to ensure the delivery of a sufficient payload of drug to the vascular regions under physiologic shear stress conditions, whereby the most promising experimental results have thus far been reported with endothelial adhesion molecule-targeting and magnetic drug targeting approaches. Further studies in vitro and in vivo are necessary to determine the key factors affecting particle internalization under flowconditions.