Ilya Skachkov

Lipid Shedding from Single Oscillating Microbubbles

Lipid-coated microbubbles are used clinically as contrast agents for ultrasound imaging and are being developed for a variety of therapeutic applications. The lipid encapsulation and shedding of the lipids by acoustic driving of the microbubble has a crucial role in microbubble stability and in ultrasound-triggered drug delivery; however, little is known about the dynamics of lipid shedding under ultrasound excitation. Here we describe a study that optically characterized the lipid shedding behavior of individual microbubbles on a time scale of nanoseconds to microseconds. A single ultrasound burst of 20 to 1000 cycles, with a frequency of 1 MHz and an acoustic pressure varying from 50 to 425 kPa, was applied. In the first step, high-speed fluorescence imaging was performed at 150,000 frames per second to capture the instantaneous dynamics of lipid shedding. Lipid detachment was observed within the first few cycles of ultrasound. Subsequently, the detached lipids were transported by the surrounding flow field, either parallel to the focal plane (in-plane shedding) or in a trajectory perpendicular to the focal plane (out-of-plane shedding). In the second step, the onset of lipid shedding was studied as a function of the acoustic driving parameters, for example, pressure, number of cycles, bubble size and oscillation amplitude. The latter was recorded with an ultrafast framing camera running at 10 million frames per second. A threshold for lipid shedding under ultrasound excitation was found for a relative bubble oscillation amplitude >30%. Lipid shedding was found to be reproducible, indicating that the shedding event can be controlled.

Targeted ultrasound contrast agents for ultrasound molecular imaging and therapy

Abstract Ultrasound contrast agents (UCAs) are used routinely in the clinic to enhance contrast in ultrasonography. More recently, UCAs have been functionalised by conjugating ligands to their surface to target specific biomarkers of a disease or a disease process. These targeted UCAs (tUCAs) are used for a wide range of pre-clinical applications including diagnosis, monitoring of drug treatment, and therapy. In this review, recent achievements with tUCAs in the field of molecular imaging, evaluation of therapy, drug delivery, and therapeutic applications are discussed. We present the different coating materials and aspects that have to be considered when manufacturing tUCAs. Next to tUCA design and the choice of ligands for specific biomarkers, additional techniques are discussed that are applied to improve binding of the tUCAs to their target and to quantify the strength of this bond. As imaging techniques rely on the specific behaviour of tUCAs in an ultrasound field, it is crucial to understand the characteristics of both free and adhered tUCAs. To image and quantify the adhered tUCAs, the state-of-the-art techniques used for ultrasound molecular imaging and quantification are presented. This review concludes with the potential of tUCAs for drug delivery and therapeutic applications.

Intravital microscopy of localized stem cell delivery using microbubbles and acoustic radiation force

The use of stem cells for the repair of damaged cardiac tissue after a myocardial infarction holds great promise. However, a common finding in experimental studies is the low number of cells delivered at the area at risk. To improve the delivery, we are currently investigating a novel delivery platform in which stem cells are conjugated with targeted microbubbles, creating echogenic complexes dubbed StemBells. These StemBells vibrate in response to incoming ultrasound waves making them susceptible to acoustic radiation force. The acoustic force can then be employed to propel circulating StemBells from the centerline of the vessel to the wall, facilitating localized stem cell delivery. In this study, we investigate the feasibility of manipulating StemBells acoustically in vivo after injection using a chicken embryo model. Bare stem cells or unsaturated stem cells (<5 bubbles/cell) do not respond to ultrasound application (1 MHz, peak negative acoustical pressure P_ = 200 kPa, 10% duty cycle). However, stem cells which are fully saturated with targeted microbubbles (>30 bubbles/cell) can be propelled toward and arrested at the vessel wall. The mean translational velocities measured are 61 and 177 μm/s for P‐ = 200 and 450 kPa, respectively. This technique therefore offers potential for enhanced and well‐controlled stem cell delivery for improved cardiac repair after a myocardial infarction. Biotechnol. Bioeng. 2015;112: 220–227.

Imaging Microvasculature with Contrast-Enhanced Ultraharmonic Ultrasound

Atherosclerotic plaque neovascularization was shown to be one of the strongest predictors of future cardiovascular events. Yet, the clinical tools for coronary wall microvasculature detection in vivo are lacking. Here we report an ultrasound pulse sequence capable of detecting microvasculature invisible in conventional intracoronary imaging. The method combines intravascular ultrasound with an ultrasound contrast agent, i.e., a suspension of microscopic vascular acoustic resonators that are small enough to penetrate the capillary bed after intravenous administration. The pulse sequence relies on brief chirp excitations to extract ultraharmonic echoes specific to the ultrasound contrast agent. We implemented the pulse sequence on an intravascular ultrasound probe and successfully imaged the microvasculature of a 6 days old chicken embryo respiratory organ. The feasibility of microvasculature imaging with intravascular ultrasound sets the stage for a translation of the method to studies of intra-plaque neovascularization detection in humans.

Targeted microbubble mediated sonoporation of endothelial cells in vivo

Ultrasound contrast agents as drug-delivery systems are an emerging field. Recently, we reported that targeted microbubbles are able to sonoporate endothelial cells in vitro. In this study, we investigated whether targeted microbubbles can also induce sonoporation of endothelial cells in vivo, thereby making it possible to combine molecular imaging and drug delivery. Live chicken embryos were chosen as the in vivo model. αvß3-targeted microbubbles attached to the vessel wall of the chicken embryo were insonified at 1 MHz at 150 kPa (1 × 10 000 cycles) and at 200 kPa (1 × 1000 cycles) peak negative acoustic pressure. Sonoporation was studied by intravital microscopy using the model drug propidium iodide (PI). Endothelial cell PI uptake was observed in 48% of microbubble-vessel-wall complexes at 150 kPa (n = 140) and in 33% at 200 kPa (n = 140). Efficiency of PI uptake depended on the local targeted microbubble concentration and increased up to 80% for clusters of 10 to 16 targeted microbubbles. Ultrasound or targeted microbubbles alone did not induce PI uptake. This intravital microscopy study reveals that sonoporation can be visualized and induced in vivo using targeted microbubbles.

Viability of endothelial cells after ultrasound-mediated sonoporation: Influence of targeting, oscillation, and displacement of microbubbles

Microbubbles (MBs) have been shown to create transient or lethal pores in cell membranes under the influence of ultrasound, known as ultrasound-mediated sonoporation. Several studies have reported enhanced drug delivery or local cell death induced by MBs that are either targeted to a specific biomarker (targeted microbubbles, tMBs) or that are not targeted (non-targeted microbubbles, ntMBs). However, both the exact mechanism and the optimal acoustic settings for sonoporation are still unknown. In this study we used real-time uptake patterns of propidium iodide, a fluorescent cell impermeable model drug, as a measure for sonoporation. Combined with high-speed optical recordings of MB displacement and ultra-high-speed recordings of MB oscillation, we aimed to identify differences in MB behavior responsible for either viable sonoporation or cell death. We compared ntMBs and tMBs with identical shell compositions exposed to long acoustic pulses (500-50,000cycles) at various pressures (150-500kPa). Propidium iodide uptake highly correlated with cell viability; when the fluorescence intensity still increased 120s after opening of the pore, this resulted in cell death. Higher acoustic pressures and longer cycles resulted in more displacing MBs and enhanced sonoporation. Non-displacing MBs were found to be the main contributor to cell death, while displacement of tMBs enhanced reversible sonoporation and preserved cell viability. Consequently, each therapeutic application requires different settings: non-displacing ntMBs or tMBs are advantageous for therapies requiring cell death, especially at 500kPa and 50,000cycles, whereas short acoustic pulses causing limited displacement should be used for drug delivery.

Quantification of bound microbubbles in ultrasound molecular imaging

Molecular markers associated with diseases can be visualized and quantified noninvasively with targeted ultrasound contrast agent (t-UCA) consisting of microbubbles (MBs) that can bind to specific molecular targets. Techniques used for quantifying t-UCA assume that all unbound MBs are taken out of the blood pool few minutes after injection and only MBs bound to the molecular markers remain. However, differences in physiology, diseases, and experimental conditions can increase the longevity of unbound MBs. In such conditions, unbound MBs will falsely be quantified as bound MBs. We have developed a novel technique to distinguish and classify bound from unbound MBs. In the post-processing steps, first, tissue motion was compensated using block-matching (BM) techniques. To preserve only stationary contrast signals, a minimum intensity projection (MinIP) or 20th-percentile intensity projection (PerIP) was applied. The after-flash MinIP or PerIP was subtracted from the before-flash MinIP or PerIP. In this way, tissue artifacts in contrast images were suppressed. In the next step, bound MB candidates were detected. Finally, detected objects were tracked to classify the candidates as unbound or bound MBs based on their displacement. This technique was validated in vitro, followed by two in vivo experiments in mice. Tumors (n = 2) and salivary glands of hypercholesterolemic mice (n = 8) were imaged using a commercially available scanner. Boluses of 100 μL of a commercially available t-UCA targeted to angiogenesis markers and untargeted control UCA were injected separately. Our results show considerable reduction in misclassification of unbound MBs as bound ones. Using our method, the ratio of bound MBs in salivary gland for images with targeted UCA versus control UCA was improved by up to two times compared with unprocessed images.

Surface contact of bound targeted microbubbles

For molecular imaging using ultrasound contrast agents, targeted microbubbles are designed with specific ligands linked to the coated shell. Research is ongoing to determine the binding force of targeted microbubbles and to distinguish bound from unbound targeted microbubbles using ultrasound. For this, the actual surface of the targeted microbubbles that binds to a pathology is important. This study focuses on determining the surface contact of bound targeted microbubbles by fluorescence microscopy. Biotinylated lipid-coated microbubbles (3-7 μm in diameter) with either DSPC or DPPC as the main lipid were targeted to a streptavidin-coated surface. The binding area of targeted microbubbles was found to be 6 ± 4% of the total microbubble surface for microbubbles with DSPC as the main lipid (n=22) and 11 ± 4% for microbubbles with DPPC as the main lipid (n=24). The difference can be explained by the heterogeneous distribution of the ligand for DSPC microbubbles whereas the ligand is homogeneously distributed for DPPC microbubbles. These findings can be used to improve the binding of targeted microbubbles and for the ongoing research to distinguish bound from unbound microbubbles.

Liposome shedding from a vibrating microbubble on nanoseconds timescale

When ultrasound contrast agents microbubbles (MBs) are preloaded with liposomes, they can be applied as a potential drug delivery vehicle. The fate of the liposomes under ultrasound excitations is of prime interest for investigations, since it is an essential step in the application of drug delivery. Previous studies on regular lipid-shelled MBs have shown lipid shedding phenomena, accompanied by MB shrinkage under ultrasound excitations. Here we present a multi-modal study to optically characterize shedding behavior of liposome-loaded MBs (lps-MBs) based on high-speed fluorescence imaging. First, the dynamics of shedding were resolved by the Brandaris camera operating at up to 2 million frames per second (Mfps). Shedding of shell material was observed after few cycles of the excitation pulse. Second, a parametric study using a Photron camera running at 75 kfps indicates a significant influence of MB resonance on the shedding behavior. Third, the shedding behavior was investigated as a function of the MB oscillatory dynamics, facilitated by combination of the two fast cameras. We found a threshold of the relative amplitude of oscillations (35%) for the onset of lipids shedding. Overall, the shedding behavior from lps-MBs could well be controlled by the excitation pulse.

Optimization of ultrasound contrast agent for high frequency ultrasound molecular imaging using subharmonic oscillation

Ultrasound molecular imaging visualizes disease biomarkers using targeted ultrasound contrast agents (t-UCA). Different lipids result in UCA with different acoustic behavior. In this study, subharmonic (SH) response of MicroMarker UCA and four homemade UCA with different lipid coatings were compared in vitro with a high frequency ultrasound system (Vevo 2100 with MS250 probe). UCA with different size distribution were made with DSPC (UCA A and C) or DPPC (UCA B and D) as main lipid by sonication or Vialmix. We transmitted long bursts (20-cycle, 30 MHz, 10% power, MS250 probe) with pulse inversion sequence for optimized SH imaging. The effect of the UCA concentration on SH imaging was tested using two concentrations: 8.0×106 and 4.0×105 microbubbles per milliliter. For A, B and D type UCA, attenuation effect is dominant at high concentration. MicroMarker and C type UCA had the highest and most spatially homogeneous distribution of SH response throughout the entire UCA area at high concentration. SH amplitude of MicroMarker dropped about 11 dB when UCA concentration was reduced by a factor of 20. For this low concentration, SH amplitude of B type UCA was 10 dB higher than that for MicroMarker and was homogeneous throughout the UCA area. We showed that for 30 MHz transmit frequency, at low concentration of UCA, DPPC microbubbles have higher SH response than DSPC ones and at high concentration, smaller bubbles (MicroMarker and C) produced the most homogeneous SH responses. Our results suggest that for molecular imaging applications where UCA concentration is low, our B-type and MicroMarker UCA are suitable choices for SH imaging.