Idarubicin-loaded ONCOZENE drug-eluting embolic agents for chemoembolization of hepatocellular carcinoma: in vitro loading and release and in vivo pharmacokinetics.

PURPOSE: To present in vitro loading and release characteristics of idarubicin with ONCOZENE (CeloNova BioSciences, Inc, San Antonio, Texas) drug-eluting embolic (DEE) agents and in vivo pharmacokinetics data after transarterial chemoembolization with idarubicin-loaded ONCOZENE DEE agents in patients with hepatocellular carcinoma. MATERIALS AND METHODS: Loading efficacy of idarubicin with ONCOZENE DEE agents 100 µm and DC Bead (Biocompatibles UK Ltd, Farnham, United Kingdom) DEE agents 100-300 µm was monitored at 10, 20, and 30 minutes loading time by high-pressure liquid chromatography. A T-apparatus was used to monitor the release of idarubicin from the two types of DEE agents over 12 hours. Clinical and 24-hour pharmacokinetics data were recorded after transarterial chemoembolization with idarubicin-loaded ONCOZENE DEE agents in four patients with unresectable hepatocellular carcinoma. RESULTS: Idarubicin loading in ONCOZENE DEE agents was > 99% at 10 minutes. Time to reach 75% of the release plateau level was 37 minutes ± 6 for DC Bead DEE agents and 170 minutes ± 19 for ONCOZENE DEE agents both loaded with idarubicin 10 mg/mL. After transarterial chemoembolization with idarubicin-loaded ONCOZENE DEE agents, three partial responses and one complete response were observed with only two asymptomatic grade 3 biologic adverse events. Median time to maximum concentration for idarubicin in patients was 10 minutes, and mean maximum concentration was 4.9 µg/L ± 1.7. Mean area under the concentration-time curve from 0-24 hours was equal to 29.5 µg.h/L ± 20.5. CONCLUSIONS: ONCOZENE DEE agents show promising results with very fast loading ability, a favorable in vivo pharmacokinetics profile with a sustained release of idarubicin during the first 24 hours, and encouraging safety and responses. Histopathologic and clinical studies are needed to evaluate idarubicin release around the DEE agents in tumor tissue and to confirm safety and efficacy.

Polymeric substrates with tunable elasticity and nanoscopically controlled biomolecule presentation.

Despite tremendous progress in recent years, nanopatterning of hydrated polymeric systems such as hydrogels still represents a major challenge. Here, we employ block copolymer nanolithography to arrange gold nanoparticles on a solid template, followed by the transfer of the pattern to a polymeric hydrogel. In the next step, these nanoparticles serve as specific anchor points for active biomolecules. We demonstrate the engineering of poly(ethylene glycol) hydrogel surfaces with respect to elasticity, nanopatterning, and functionalization with biomolecules. For the first time, biomolecule arrangement on the nanometer scale and substrate stiffness can be varied independently from each other. Young's moduli, a measure of the compliance of the substrates, can be tuned over 4 orders of magnitude, including the values for all of the different tissues found in the human body. Structured hydrogels can be used to pattern any histidine-tagged protein as exemplified for his-protein A as an acceptor for immunoglobulin. When cell-adhesion-promoting peptide cRGDfK is selectively coupled to gold nanoparticles, the surfaces provide cues for cell-surface interaction and allow for the study of the modulation of cellular adhesion by the mechanical properties of the environment. Therefore, these substrates represent a unique multipurpose platform for studying receptor/ligand interactions with adhering cells, mechanotransduction, and cell-adhesion-dependent signaling.

Cell interactions with hierarchically structured nano-patterned adhesive surfaces.

The activation of well-defined numbers of integrin molecules in predefined areas by adhesion of tissue cells to biofunctionalized micro-nanopatterned surfaces was used to determine the minimum number of activated integrins necessary to stimulate focal adhesion formation. This was realized by combining micellar and conventional e-beam lithography, which enabled deposition of 6 nm large gold nanoparticles on predefined geometries. Patterns with a lateral spacing of 58 nm and a number of gold nanoparticles, ranging from 6 to 3000 per adhesive patch, were used. For α(v) ß(3)-integrin activation, gold nanoparticles were coated with c(-RGDfK-)-thiol peptides, and the remaining glass surface was passivated to prevent non-specific protein adsorption and cell adhesion. Results show that focal adhesion formation is dictated by the underlying hierarchical nanopattern. Adhesive patches with side lengths of 3000 nm and separated by 3000 nm, or with side lengths of 1000 nm and separated by 1000 nm, containing approximately 3007 ± 193 or 335 ± 65 adhesive gold nanoparticles, respectively, induced the formation of actin-associated, paxillin-rich focal adhesions, comparable in size and shape to classical focal adhesions. In contrast, adhesive patches with side lengths of 500, 250 or 100 nm, and separated from adjacent adhesive patches by their respective side lengths, containing 83 ± 11, 30 ± 4, or 6 ± 1 adhesive gold nanoparticles, respectively, showed a significant increase in paxillin domain length, caused by bridging the pattern gap through an actin bundle in order to mechanically, synergistically strengthen each single adhesion site. Neither paxillin accumulation nor adhesion formation was induced if less than 6 c(-RGDfK-)-thiol functionalised gold nanoparticles per adhesion site were presented to cells.

Induction of cell polarization and migration by a gradient of nanoscale variations in adhesive ligand spacing.

Cell interactions with adhesive surfaces play a vital role in the regulation of cell proliferation, viability, and differentiation, and affect multiple biological processes. Since cell adhesion depends mainly on the nature and density of the adhesive ligand molecules, spatial molecular patterning, which enables the modulation of adhesion receptor clustering, might affect both the structural and the signaling activities of the adhesive interaction. We herein show that cells plated on surfaces that present a molecularly defined spacing gradient of an integrin RGD ligand can sense small but consistent differences in adhesive ligand spacing of about 1 nm across the cell diameter, which is approximately 61 mum when the spacing includes 70 nm. Consequently, these positional cues induce cell polarization and initiate cell migration and signaling. We propose that differential positional clustering of the integrin transmembrane receptors is used by cells for exploring and interpreting their environment, at high spatial sensitivity.

Actin-cytoskeleton dynamics in non-monotonic cell spreading.

The spreading of motile cells on a substrate surface is accompanied by reorganization of their actin network. We show that spreading in the highly motile cells of Dictyostelium is non-monotonic, and thus differs from the passage of spreading cells through a regular series of stages. Quantification of the gain and loss of contact area revealed fluctuating forces of protrusion and retraction that dominate the interaction of Dictyostelium cells with a substrate. The molecular basis of these fluctuations is elucidated by dual-fluorescence labeling of filamentous actin together with proteins that highlight specific activities in the actin system. Front-to-tail polarity is established by the sorting out of myosin-II from regions where dense actin assemblies are accumulating. Myosin-IB identifies protruding front regions, and the Arp2/3 complex localizes to lamellipodia protruded from the fronts. Coronin is used as a sensitive indicator of actin disassembly to visualize the delicate balance of polymerization and depolymerization in spreading cells. Short-lived actin patches that co-localize with clathrin suggest that membrane internalization occurs even when the substrate-attached cell surface expands. We conclude that non-monotonic cell spreading is characterized by spatiotemporal patterns formed by motor proteins together with regulatory proteins that either promote or terminate actin polymerization on the scale of seconds.

Protein repellent properties of covalently attached PEG coatings on nanostructured SiO(2)-based interfaces.

In this study, we report the systematic comparison of different poly(ethylene glycol) (PEG) self-assembled monolayers on glass with respect to their protein adsorption and cell adhesion resistance. Combining PEGylation with micellar nanolithography allowed the formation of gold nanoparticle arrays on glass and selective coverage of the free glass area by PEG. The gold nanoparticles serve as anchor points for the attachment of individual proteins and peptides such as the cell-matrix adhesion promoting cyclic RGDfK motif or the kinesin motor protein Eg5. The capability of the motor protein to bind microtubules remained unaffected by the immobilization. It was shown that the film thickness of a water swollen PEG layer is crucial to maximize the interaction between proteins and peptides with the nanostructures. Non-specific interaction between cells or microtubules and the surface was minimized. The optimum PEG layer thickness correlated with the size of gold nanoparticles which was approximately 5 nm.

Lateral spacing of integrin ligands influences cell spreading and focal adhesion assembly.

Cell-extracellular matrix (cell-ECM) interactions mediated by integrin receptors are essential for providing positional and environmental information necessary for many cell functions, such as proliferation, differentiation and survival. In vitro studies on cell adhesion to randomly adsorbed molecules on substrates have been limited to sub-micrometer patches, thus preventing the detailed study of structural arrangement of integrins and their ligands. In this article, we illustrate the role of the distance between integrin ligands, namely the RGD (arginine-glycine-aspartate) sequence present in ECM proteins, in the control of cell adhesion. By using substrates, which carry cyclic RGD peptides arranged in highly defined nanopatterns, we investigated the dynamics of cell spreading and the molecular composition of adhesion sites in relation to a fixed spacing between the peptides on the surface. Our novel approach for in vitro studies on cell adhesion indicates that not only the composition, but also the spatial organization of the extracellular environment is important in regulating cell-ECM interactions.

Tuning surface energies with nanopatterned substrates.

A novel approach to varying the surface energy of biofunctional substrates has been developed, where surface energies are controlled by utilizing tunable nanopatterned substrates. In this study we functionalized the nanopattern with streptavidin, providing an adhesive interface for biotinylated probes. To obtain the surface energies, we applied the Johnson-Kendall-Roberts model to the adhesion-induced deformation of elastic beads. The results reveal a linear relationship between surface energy and ligand density, demonstrating the capability of this technique to adjust surface energy.

Activation of integrin function by nanopatterned adhesive interfaces.

To study the function behind the molecular arrangement of single integrins in cell adhesion, we designed a hexagonally close-packed rigid template of cell-adhesive gold nanodots coated with cyclic RGDfK peptide by using block-copolymer micelle nanolithography. The diameter of the adhesive dots is < 8 nm, which allows the binding of one integrin per dot. These dots are positioned with high precision at 28, 58, 73, and 85 nm spacing at interfaces. A separation of > or = 73 nm between the adhesive dots results in limited cell attachment and spreading, and dramatically reduces the formation of focal adhesion and actin stress fibers. We attribute these cellular responses to restricted integrin clustering rather than insufficient number of ligand molecules in the cell-matrix interface since "micro-nanopatterned" substrates consisting of alternating fields with dense and no nanodots do support cell adhesion. We propose that the range between 58-73 nm is a universal length scale for integrin clustering and activation, since these properties are shared by a variety of cultured cells.