Microbubbles are the most commonly used imaging contrast agent in ultrasound. However, due to their size, they are limited to vascular compartments. These microbubbles can be condensed or formulated as perfluorocarbon nanodroplets (PFCnDs) that are small enough to extravasate and then be triggered acoustically at the target site. These nanoparticles can be further enhanced by including an optical absorber such as near infrared organic dye or nanoparticles (e.g., copper sulfide nanoparticles or gold nanoparticles/nanorods). Optically tagged PFCnDs can be vaporized through laser irradiation in a process known as optical droplet vaporization (ODV). This process of activation enables the use of high boiling point perfluorocarbon cores, which cannot be vaporized acoustically under the maximum mechanical index threshold for diagnostic imaging. Higher boiling point cores result in droplets that will recondense after vaporization, resulting in "blinking" PFCnDs that briefly produce contrast after vaporization before condensing back into nanodroplet form. This process can be repeated to produce contrast on demand, allowing for the background free imaging, multiplexing, super-resolution, and contrast enhancement through both optical and acoustic modulation. This article will demonstrate how to synthesize optically-triggerable, lipid shell PFCnDs utilizing probe sonication, create polyacrylamide phantoms to characterize the nanodroplets, and acoustically modulate the PFCnDs after ODV to improve contrast.
Microbubbles are the most ubiquitous ultrasound contrast agent owing to their biocompatibility and excellent echogenicity in comparison to soft tissues. This makes them valuable tools for visualizing blood flow, organ delineation, and other applications1. However, their size (1-10 µm), which makes them exceptional for imaging based on their resonant frequency, restricts their applications to the vasculature2.
This limitation has led to the development of PFCnDs, which are nano-emulsions composed of a surfactant encased around a liquid perfluorocarbon core. These nanoparticles can be synthesized at sizes as small as 200 nm and are designed to take advantage of "leaky" vasculature or pores and open fenestrations found in tumor vasculature. While these disruptions are tumor dependent, this permeability allows for extravasation of nanoparticles from ~200 nm - 1.2 µm depending on the tumor3,4. In their initial form, these particles produce little to no ultrasound contrast. Upon vaporization - induced acoustically or optically - the core phase changes from liquid to gas, inducing a two and half to five-fold increase in diameter5,6,7 and generating photoacoustic and ultrasound contrast. While acoustic vaporization is the most common activation method, this approach creates acoustic artifacts that limits the imaging of the vaporization. Additionally, most perfluorocarbons require focused ultrasound with a mechanical index beyond the safety threshold to vaporize8. This has led to the development of lower boiling point PFCnDs, which can be synthesized by condensing microbubbles into nanodroplets9. However, these droplets are more volatile and subject to spontaneous vaporization10.
Optical droplet vaporization (ODV), on the other hand, requires the addition of an optical trigger such as nanoparticles11,12,13 or dye6,14,15 and can vaporize higher boiling point perfluorocarbons using fluences within the ANSI safety limit11. PFCnDs synthesized with higher boiling point cores are more stable and will recondense after vaporization, allowing for background free imaging16, multiplexing17, and super-resolution18. One of the major limitations of these techniques is the fact that high boiling point PFCnDs are echogenic after vaporization for only a short timeframe, on the scale of milliseconds19, and are relatively faint. While this issue can be mitigated through repeated vaporizations and averaging, detection and separation of droplet signal remains a challenge.
Taking inspiration from pulse inversion, the duration and contrast can be enhanced by modifying the phase of the ultrasound imaging pulse19. By starting the ultrasound imaging pulse with a rarefaction phase (n-pulse), both the duration and contrast of the vaporized PFCnDs increases. In contrast, starting the ultrasound imaging pulse with a compression phase (p-pulse), results in reduced contrast and shorter in duration. This article will describe how to synthesize optically triggerable perfluorocarbon nanodroplets, polyacrylamide phantoms commonly used in imaging, and demonstrate contrast enhancement and improved signal longevity through acoustic modulation.
1. Perfluorocarbon nanodroplet formulation
- Rinse out a 10 mL round-bottom flask with chloroform and wash out a 10 µL and 1 mL gas tight glass syringe with chloroform by repeatedly aspirating the full syringe volume and expelling it for a total of three times.
CAUTION: Chloroform is volatile and can be toxic if inhaled. All work with this solvent should be performed in a fume hood.
- Using the syringes, add 200 µL of DSPE-mPEG2000 (25 mg/mL), 6.3 µL of 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC, 25 mg/mL) and 1 mL of IR 1048 (1 mg/mL in chloroform) into the round-bottom flask. Remember to clean out the syringes between lipids/dye to prevent contamination of the stock.
NOTE: Infrared dyes are light sensitive, and work should be done in dim conditions or flasks should be covered in aluminum foil.
- Remove the solvent utilizing a rotary evaporator. Ensure that the vacuum is slowly adjusted to 332 mbar to prevent bumping. After 5 min, reduce the pressure to 42 mbar to remove any water that may have entered the solution.
NOTE: The lipid cake can be stored overnight in a round bottom flask covered with parafilm at 4 °C.
- Suspend the lipid cake in 1 mL of phosphate buffered saline (PBS) and sonicate or vortex at room temperature for 5 min or until all of the lipid cake has been suspended and dissolved in the solution. Sonicate for an additional 2 min to homogenize the solution.
- Transfer the solution to a 7 mL glass vial and place the vial in a glass dish filled with ice to allow the solution to cool down for 5 min before adding 50 µL of perfluorohexane using a gas tight glass syringe. Remember to rinse out the syringe with perfluorohexane before dispensing it into the vial.
- Place the glass vial containing the lipids and ice bath in the probe sonicator enclosure and submerge the probe tip below the miniscus. Ensure that the sides of the sonicator probe does not touch the lip of the glass vial.
- Probe sonicate the mixture with the following settings: Amplitude 1, Process time: 20 s, Pulse-On: 1s, Pulse-off: 5s. Then sonicate at the following settings: Amplitude: 50, Process time: 5 s, Pulse-on: 1 s, Pulse-off: 10 s.
- Transfer the nanodroplet solution to a 1.5 mL centrifuge tube and centrifuge at 300 x g for 3 min to separate out the larger droplets (>1 µm) from smaller droplets.
- Discard the pellet and transfer the supernatant to another 1.5 mL centrifuge tube. Wash the supernatant by centrifuging at 3000 x g for 5 min to pellet all the droplets in solution. Resuspend the PFCnDs in 1 mL of PBS by pipetting the pellet up and down and then sonicate in a bath sonicator for 1 min.
- Measure the size of the droplets using dynamic light scattering (DLS). Dilute the stock PFCnDs by 100-fold (10 µL of PFCnD stock in 990 µL of PBS) and bath sonicate to disperse the PFCnDs before measuring. Representative results are shown in Figure 1.
- Determine the concentration of the PFCnDs utilizing the nanoparticle tracking analyzer (see Table of Materials). Dilute the PFCnDs by 100-1000-fold to ensure accurate measurement of the concentration. The protocol typically yields droplets at a concentration on the order of 1010 particles/mL.
- Prepare 10 mL of ultrasound coupling gel in a 50 mL centrifuge tube and add 1% (v/v) or 100 µL of PFCnDs to make solution of ~108 particles/mL. Vortex the solution to mix. Centrifuge the mixture at 4000 x g for 3 min to remove bubbles.
2. Polyacrylamide phantom preparation
- Degas water by filling a 500 mL vacuum flask with 400 mL of deionized water, seal with a rubber cork, and connect the flask to the vacuum line. Open the vacuum line and submerge the bottom of the flask in the bath sonicator. Sonicate for 5 min or until no gas bubble formation is visible.
- Prepare 10% ammonium persulfate (APS) solution by dissolving 500 mg in 5 mL of degassed water. Gently swirl the solution if the ammonium persulfate does not fully dissolve.
- In a 400 mL beaker with a stir bar on a stir plate, add 150 mL of degassed water and 50 mL of 40% (w/v) acrylamide-bisacrylamide solution to form 200 mL of 10% acrylamide-bisacrylamide solution. Stir the mixture at 200 rpm to allow for the proper mixing without introducing bubbles.
CAUTION: Acrylamide is a carcinogen, and all work should be done in a fume hood with gloves, especially if working with acrylamide in powder form.
- Weigh out 400 mg of silica to and add it to the 10% acrylamide-bisacrylamide solution from step 2.3 to form a 0.2 %(w/v) of silica and acrylamide solution.
CAUTION: Silica when inhaled can be a carcinogen. All work including weighing should be performed in a fume hood.
- Prepare a 58 mm x 58 mm x 78 mm square mold with a cylindrical inclusion by cutting off the tips of from a plastic transfer pipette and supporting it in the mold with lab tape. See Figure 2.
- Add 2 mL of 10 % APS solution to the beaker to make a final concentration of 0.1% APS and add 250 µL of Tetramethylethylenediamine (TEMED) to the phantom solution. Allow the solution to stir briefly (less than a min).
- Quickly pour the solution into the mold, while being careful not to introduce air bubbles into the solution. The solution should polymerize within 10 min. Remove the phantom by running the flat end of a lab spatula around the edge of the mold and inverting the mold.
NOTE: These phantoms can be reused multiple times and should be submerged in water and stored at 4°C.
3. Perfluorocarbon nanodroplet imaging
- Turn on and warm up the pulsed laser system for ~20 min following manufacturer instructions. Ensure that the fiber optical bundle is properly connected to the laser output and the two legs are properly placed within the fiber bundle holder.
- Turn on the ultrasound imaging system, connect array imaging transducer (L11-4v) to the system and fix the transducer within the holder to align its imaging plane with laser cross section.
- Set the pulse repetition frequency of the laser system to 10Hz and place a powermeter at the end of the fiber bundle to measure energy. Tune the q-switch delay until the estimated fluence is 70 mJ/cm2.
CAUTION: Appropriate eyewear must be worn when firing the laser and laser curtains must enclose the space.
- Backfill one of the channels in the polyacrylamide phantom with the ultrasound gel/PFCnD mixture using a 1 mL plastic slip tip syringe. Liberally cover the top of the channel with ultrasound gel and remove any bubbles with a 1 mL plastic slip tip syringe. Place the polyacrylamide phantom underneath the transducer and fiber bundle as shown in Figure 3.
- Use the combined laser ultrasound and elasticity (CLUE) imaging platform based on the software20 to image PFCnD synchronized with optical activation. Change the general user-defined parameters in Param structure for imaging: set start/end depth to 0/40mm, center frequency to 6.9MHz, and transducer name to 'L11-4v'.
- Define a new RunCase and design a module sequence for repeated optical activation/recondensation and US imaging of PFHnDs. This is done by listing predefined modules such as ultrafast imaging (mUF), external laser (mExtLaser) and idle(mIdle).
- Repeat the sequence set mExtLaser-mIdle-mUF-mExtLaser-mUF twice to acquire both n-pulse and p-pulse imaging data.
NOTE: The first mExtLaser module in each sequence is set as a sham laser by setting ExtLaser.Enable to 0 and the 'mIdle' is included to minimize time between background US images and the n/p-pulse US images after laser activation.
- Repeat the sequence set mExtLaser-mIdle-mUF-mExtLaser-mUF twice to acquire both n-pulse and p-pulse imaging data.
- Set module parameters for each module placed in the current run case's module sequence. Access each module parameter by index corresponding to its order in module sequence. Modules will execute pre-defined operations with module parameters user set here.
- Set ExtLaser.QSdelay in external laser modules to the value of laser Q-switch delay tuned in step 3.3, in microseconds. This module waits for laser system's flashlamp trigger out and generates Q-switch trigger after the delay specified in QSdelay.
- In ultrafast imaging module, set Resource.numFrame to 100, set SeqControl.PRI to 200 (µs), and set TW.polarity to 1 for P-pulse and -1 for N-pulse (see Figure 4 for corresponding pulse shape). This module will transmit ultrafast 0-degree planar wave with pulse type specified in TW.polarity.
- Acquire full aperture imaging window of 38.8 mm wide for number of frames in Resource.numFrame, pulse repetition interval of SeqControl.PRI, then save data for off-line processing.
- Set SeqControl.lastPRI_Module in idle module to the length of time between laser pulses (100 ms) subtracted by Q-switch delay, imaging data acquisition time (20 ms), and a 20 µs margin for the signal to travel. This module keeps the system under 'no operation' state for the time in SeqControl.lastPRI_Module to fill the time gap between the end of imaging data acquisition and next laser pulse excitation.
Successful formulation and centrifugal separation of the PFCnDs should yield droplets around the size of 200-300 nm in diameter (Figure 1A). Improperly separated droplets may show small peaks around 1 µm. These solutions can be further bath sonicated to break up the larger droplets. The size of the droplets will increase over time due to coalescing and/or diffusion in a process known as Ostwald ripening21,22 (Figure 1B).
Acoustic modulation of the droplets by manipulating the imaging pulse improved the contrast of the vaporized PFCnDs. This was demonstrated in PFCnD images reconstructed by subtracting adjacent frames of the beamformed images so that only the signal returned from vaporized PFCnD is visible and stationary background signal is suppressed. Contrast is quantified by the ratio of the difference between average signals of the circular inclusion area and average background signal over average background signal. The background signal is defined by the signals from two rectangular ROIs of the background that are at the same depth and equivalent area as the inclusions. The contrast from the inclusion for the N-pulse is approximately 3.2 times greater (i.e., 220 % improvement) than the P-pulse (Figure 5).
The inversed imaging pulse also increased the longevity of the signal from PFCnD vaporization. This was quantified by thresholding the pixels in the circular inclusion region that exceeds the background signal. The percentage of pixels in the inclusion that was above the threshold was defined as the hyperechoic area (%). To examine the PFCnDs' hyperechogenic behavior over time, hyperechoic area is calculated for each frame and normalized by the hyperechoic area of the first frame, and then fitted to an exponential decay model. This function was used to determine the characteristic decay time, defined as the timespan it takes for the hyperechoic area after PFCnD activation to decay to only 10 % of the initial area (Figure 6a). The characteristic decay time of normalized hyperechoic area is up to 3.5 times longer in N-pulse imaging compared to P-pulse. Representative B-mode differential image frames in time for each N-pulse and P-pulse imaging are shown in Figure 6b.
Figure 1: DLS size measurements of PFCnDs and stability. (A) The size intensity distribution of droplets averaged from three measurements of droplets after synthesis (average PDI: 0.132± 0.016; average Z-average: 259.3 ± 0.7 nm). (B) The size intensity distribution of droplets averaged from three measurements taken 24 hours after synthesis (average PDI: 0.252± 0.061; average Z-average: 322.5 ± 4.5 nm). Please click here to view a larger version of this figure.
Figure 2: Image and schematic of polyacrylamide mold. (A) Image of the mold made from lab tape and the plastic container. (B) Schematic with measurements of the polyacrylamide phantom after removal from mold. Please click here to view a larger version of this figure.
Figure 3: A schematic of the laser pulse delivery and ultrasound imaging. (A) Components of the assembly are labeled and laser beam / ultrasound imaging plane alignment relative to the inclusion position is illustrated. (B) An image showing the actual setup. Please click here to view a larger version of this figure.
Figure 4: Simulated ultrasound imaging pulse. The waveforms are simulated by ultrasound imaging system software, sampled by 250 MHz. The waveform of P-pulse and N-pulse are generated with the same center frequency and pulse width but have 180˚ of phase difference. Please click here to view a larger version of this figure.
Figure 5: Contrast measurement. Mean contrast value of inclusion area for N-pulse and P-pulse, error bars represent standard deviation (n=3). Please click here to view a larger version of this figure.
Figure 6: Characteristic decay curve of hyperechoic area and representative differential B-mode mages. (A) Normalized hyperechoic area induced by PFCnD activation over time for N-pulse and P-pulse imaging at the same cross-section. The dotted line indicates 10% of the initial hyperechoic area. The time at which the fitted plot intersects with the dotted line represents the characteristic decay time. (B) Images show a cropped ROI window centered on the inclusion, plotted on a dB scale with a dynamic range of 35. The top row shows the recondensing behavior imaged by the P-pulse and the lower row shows the N-pulse. The yellow-colored dashed line indicates the inclusion area. Please click here to view a larger version of this figure.
|Total Volume of Phantom (mL)||50||100||250||500|
|DI water (mL)||37.5||74.9||187.4||375|
|40% PA solution (mL)||12.5||25.1||62.6||125|
|10% APS solution (µL)||500||1000||2500||5000|
Table 1: Summary of the reagents and amounts for polyacrylamide phantom crosslinking based on mold volume. This table provides a concise value summary of the reagents used and amounts based upon several common mold volumes.
Probe sonication is a relatively simple and easy to learn method to fabricate PFCnDs. There are a few steps where care must be taken. When handling chloroform, it is imperative that a positive displacement pipette or glass syringes is used, as it is volatile and will "leak" from standard air displacement pipettes. Furthermore, if using a positive displacement, ensure that an appropriate tip is used as chloroform will dissolve most plastic tips, which can introduce contaminants into the solution. A positive displacement pipette or glass syringe is also recommended for perfluorohexane, as it is both volatile and denser than water. Typically, the individual effects of volatility and high density can be reduced by pre-wetting in air displacement pipettes and using a scale to adjust the volume set on the pipette, respectively. But in the case of perfluorohexane which possesses both properties, the volatility will make it difficult to obtain accurate weight measurements, making a positive displacement pipette/glass syringe the most viable option.
Before probe sonicating the solution, it is important to incubate the lipid and perfluorocarbon solution in an ice bath to allow it to cool down to prevent boiling the perfluorocarbon during sonication. This step will be especially important for lower boiling perfluorocarbon such as perfluoropentane. Furthermore, care must be taken when probe sonicating the solution. The sonication probe tip should be submerged, but it should not make contact with the bottom or sides of the glass vial as it could damage the tip and shatter the vial, emptying the lipid solution into the ice bath.
The PFCnD fabrication protocol can be adapted in a few minor ways. If a rotary evaporator is unavailable in step 1.3, the solution can be dried with a steady stream of nitrogen gas or be placed in a vacuum chamber overnight to form the lipid cake. Regarding the lipids, this formulation utilizes a 9:1 ratio of DSPE-PEG:DSPC compared to the standard 1:9 ratio of DSPE-PEG:DSPC, because it results in smaller and more size stable droplets23. This formulation can be adapted to allow for surface conjugation by substituting a small fraction (~2 mol %) of the DSPE-PEG with a functionalized DSPE-PEG with the desired moiety (e.g., biotin, thiol, amine, etc.).
In general, probe sonicators are commercially available, relatively simple to use, and can be easily adapted to other higher boiling point perfluorocarbons and surfactant formulations, but it cannot be used to make droplets with perfluorocarbon cores that are gaseous at room temperature without significant modifications. One such modification is utilizing probe sonication to create microbubbles and then applying pressure and reducing the temperature to condense the microbubbles into droplets24. While this method is a clever way to generate acoustically vaporizable droplets, it is difficult to encapsulate enough dye within the microbubbles to ensure ODV after condensation. An alternative approach is to conjugate the dye (e.g., Cy7.5) to the lipids and form microbubbles which can be condensed down into ODV capable low boiling point PFCnDs25.
Probe sonication also produces a high concentration of nanodroplets (~1010 droplets/mL) in a relatively short period of time. However, this technique results in a large size distribution that will reduce the amount of nanodroplets that will extravasate. While, this can be ameliorated through centrifugal filtering or syringe filters to remove larger droplets, the resulting PFCnDs will exhibit greater polydispersity in comparison to droplets synthesized using microfluidics or filtered through extrusion26. Another drawback to probe sonication is that the sonication probe tip will inevitably become pitted from cavitation during sonication and will need to be replaced periodically.
An alternative approach to creating droplets utilizes microfluidic devices which can be used to tailor droplets to a specific size with a low polydispersity index (PDI). However, these devices produce droplets at a relatively slow rate (~104-106 droplets/s)26 and, while there have been several developments such as step emulsification27, tip streaming in flow focusing devices28,29, and utilizing the ouzo effect with a staggered herringbone micromixer30 - generating nanosized droplets still remains challenging. Furthermore, this technique is not commercially available, and the fabrication of these devices requires specialized expertise.
Other methods that are commercially available include extrusion and homogenization. Extrusion utilizes membranes to pass droplets through, resulting in nano-sized droplets with a narrower size range compared to sonication. However this method is heavily formulation dependent and is challenging to incorporate dye or therapeutic cargo within the droplet26. High pressure homogenization makes use of commercially available homogenizers that utilize high pressure and shear stress to generate monodisperse, nanoscale lipid particles in a scalable fashion31,32,33. This method has been adapted to create droplets with high and low boiling point perfluorocarbons32,34. A more substantial review of droplet formulation methods and sample protocols can be found in the following review26.
Phantoms are a valuable tool to characterize the performance of nanodroplets in vitro. In this protocol, polyacrylamide-based phantoms with silica are used. The most frequent issues with polyacrylamide phantoms are related to slow or no polymerization. Slow polymerization, while less problematic, can lead to heterogeneous distribution of embedded scatter. The most common culprit for this issue is the use of old solutions of ammonium persulfate that reduce the production of free radicals that initiate the crosslinking. This can be easily addressed by making the solution fresh or not using prepared solutions that are older than one week. Another possibility is the degradation of TEMED - this will be evident in the formation of a yellow precipitate. One other common issue is the presence of air bubbles in the polymerized phantom. Proper degassing of the water and careful handling to avoid excess surface agitation should mitigate this issue. An alternative strategy would be to degas the entire solution after step 2.5. However, this should be performed in a fume hood due to the presence of acrylamide.
These phantoms are also excellent for imaging the behavior of restricted droplets to study individual droplet behavior; this can be done by adding PFCnDs into the phantom at step 2.4. Furthermore, since the crosslinking is due to a chemical reaction, relatively little heat is produced compared to a physical crosslinking based upon an upper critical solution temperature like gelatin. This reduces the probability for spontaneous vaporization of the embedded droplets.
While there are a variety of methods for synthesizing phantoms, polyacrylamide produces a relatively durable and non-degradable phantom that possess low acoustical attenuation35 and optical absorption coefficient36. These properties can be tuned to more closely mimic the acoustic and optical properties of human tissue by adjusting the concentration of the final polyacrylamide solution and through the inclusion of particles in the phantom such as silica, glass beads, or titanium dioxide36. Furthermore the mechanical properties of the phantoms can be adjusted by modifying the percentage of polymer content (i.e. percentage of acrylamide and bis(acrylamide)) and percentage of crosslinker (i.e. percentage of bis(acrylamide) in total polymer content)37. Alternative phantoms include but are not limited to agar38, gelatin39, polyvinyl alcohol (PVA)40, etc.
The critical steps for a successful imaging of activated PFCnD distribution and hyperechogenic dynamics are as follows. 1) Synchronize the laser system (activation source) and ultrasound imaging system. 2) Align the laser cross section both with target region of interest and with ultrasound imaging plane. 3) Adjust ultrasound imaging parameters proper to PFCnD imaging (i.e., framerate, pulse waveform, etc.).
The optical activation of PFCnD has a noticeable advantage over acoustically activated ones that it can evade the acoustic interference which drastically degrade the quality of ultrasound image while observing its recondensing phase in time. However, it is challenging to integrate and align the laser system with the ultrasound imaging system both spatially and temporally. The use of a 3D printed holder allows for repeatable and controlled light delivery. The light delivery can also be troubleshooted by inserting a metal rod into the inclusion in the polyacrylamide phantom as the metal rod should produce photoacoustic contrast to indicate light delivery. Temporal synchronization was achieved by building off a previously developed platform20, which allows for both synchronization of the lasing and imaging system while keeping the full programmability of Verasonics imaging system with a user-friendly interface. Additionally, the program provides real-time conventional B-mode imaging and photoacoustic imaging to assist in troubleshooting and locating the region of interest where PFCnDs are distributed. However, this setup requires an external nanosecond pulsed laser. Currently, to our knowledge, there are a few commercial systems that have integrated laser-ultrasound imaging systems that may allow for PFCnD imaging e.g., Visualsonics (Vevo LAZR, Vevo LAZR-X, Vevo 3100, Vevo F2), Endera Nexus 128, and iTheraMedical (insight 64, inVision 128, inVision 256-TF, and inVision 512-echo).
The ultrafast ultrasound imaging of the vaporizing-recondensing behavior of PFCnD suffers mainly from low sensitivity. While most common solutions for image sensitivity enhancement include multi-frame compounding, those techniques are limited by their inherent characteristic of degrading the framerate, since the PFCnD imaging is highly vulnerable for motion artifacts in that it includes time-differential process. The pulse polarity modulation in our protocol effectively addresses this problem in PFCnD imaging by leveraging the acoustic dynamics of vaporized PFCnDs to have more discriminable and prolonged image while not affecting temporal resolution at all.
While ODV allows for droplets with unique capabilities such as repeated vaporization and photoacoustic contrast, the activation method has limited depth penetration in comparison to ultrasound. As light penetration is limited, this restricts the applications to mainly superficial procedures such as a replacement for sentinel lymph node biopsy41. This limitation can potentially be bypassed through catheter based light delivery systems, allowing for activation deep in tissue. Since the contrast is acoustic, vaporization will be able to be imaged at depth comparable to ADV. An alternative activation technique may be magnetic droplet vaporization, in which magnetic contrast agents such as iron oxide nanoparticles are encapsulated within the droplet42. This will allow for the vaporization at any depth.
In the future, the capability of our protocol to image and modulate the hyperechogenic response of PFCnD at the same time can used to several applications where monitoring and manipulation of PFCnD are required. For example, longer detectable time can ameliorate the image quality of super-resolution imaging by giving larger number of frames to average. Furthermore, more precise control of PFCnD has potential to elevate the efficiency and safety of bubble-mediated therapeutics such as BBB opening and drug delivery.
The authors have nothing to disclose.
The work was supported in part by the Breast Cancer Research Foundation under grant BCRF-20-043.
|Ammonium Persulfate (APS)||VWR||97064-592|
|1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC)||Avanti Polar Lipids||850365C||Lipids, these can be purchased suspended in chloroform or in powder form. For long term storage, powder form is the best but chloroform is more practical.|
|1,2-distearoyl-sn-glycero-3-phosphoethanolamine-N-[methoxy(polyethylene glycol)-2000] (ammonium salt) (DSPE-PEG)||Avanti Polar Lipids||880120C||Lipids, these can be purchased suspended in chloroform or in powder form. For long term storage, powder form is the best but chloroform is more practical.|
|Acrylamide : Bisacrylamide solution (19:1) 40% (w/v), OmniPur®||VWR||EM-1300||acrylamide solution, lower concentration/ powder|
|L11-4v||Verasonics||-||ultrasound linear array transducer|
|Microtip 1/8"||Qsonica LLC||4418||microtip for probe sonicator|
|N, N, N′, N′ -Tetramethylethylenediamine (TEMED)||VWR||97064-902||Used to polymerize polyacrylamide by forming free radicals in the presence of ammonium persulfate|
|Nova II||Ophir-Spiricon||7Z01550||laser power meter|
|Phosphate buffered saline (PBS) tablets||VWR||97062-732||Tablets used to make PBS|
|Q500||Qsonica LLC||Q500-110||Probe sonicator|
|Silica gel||Sigma-Aldrich||288500||2-25 μm particle size|
|Tempest 30||New wave research||-||Pulsed laser system|
|Vantage 128||Verasonics||-||research ultrasound imaging system|
|Zetasizer Nano ZS||Malvern Instruments Ltd||-||Makes size measurements based on dynamic light scattering|
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- Aliabouzar, M., Kumar, K. N., Sarkar, K. Acoustic vaporization threshold of lipid-coated perfluoropentane droplets. The Journal of the Acoustical Society of America. 143, (4), 2001-2012 (2018).
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