Housing of the animals was provided by the Comparative Medicine Core Facility (CoMed, NTNU). Figure 3 was created in BioRender.com. Video recording and editing was done by Per Henning, webmaster at the Faculty for Natural Science at NTNU. The project was funded by the Norwegian University of Science and Technology (NTNU, Trondheim, Norway), Research Council of Norway (RCN 262228), Canadian Institutes of Health Research (FDN 154272), National Institute of Health (R01 EB003268), and the Temerty Chair in Focused Ultrasound Research at Sunnybrook Health Sciences Centre.

All the following experimental procedures were approved by and conducted in accordance with the Norwegian Food and Safety Authority, Sunnybrook Research Institute&#39;s Animal Care Committee, and the Canadian Council on Animal Care.
1. Material preparation
<ol>
	<li>Prepare the materials needed for the cranial window surgery and ultrasound-microbubble treatments. For chronic cranial windows, sterilized tools and materials, a sterile surgical space, and pre- and post-surgery drug administration are necessary23,24,25.</li>
	<li>Transducer and coverslip preparation
	<ol>
		<li>Check the physical integrity of the transducer: look for cracks and dents. Ensure the electrodes on the top and side of the transducer are intact.</li>
		<li>Deposit cyanoacrylate glue into a small dish. Use an applicator to spread a thin layer of glue onto the surface of the transducer.</li>
		<li>Place the transducer onto the glass coverslip. Press down firmly for 20-30 s. 
		NOTE: A 3D-printed mold can be used to facilitate the alignment of the glass coverslip with the ring transducer, ensuring firm and even pressure on the coverslip and ring transducer (Figure 2).</li>
		<li>Check for bubbles between the transducer and the coverslip. If there are bubbles, take the coverslip off and repeat from step 1.2.3., as air impedes ultrasound propagation. Cure overnight at room temperature.</li>
		<li>Once adhered to a glass coverslip, match the transducer (Figure 3). 
		NOTE: This protocol uses an in-house manufactured lead zirconate titanate ring transducer (10 mm outer diameter, 1.4 mm thickness, 1.2 mm height)35, matched to a 50 &#8486; impedance and 0&#176; phase load with a custom matching circuit. The transducer is driven at 0.82 MHz in thickness mode, producing a circular focal spot approximately 1 mm beneath the coverslip. Ring transducers of similar properties (10 mm outer diameter, 1.5 mm thickness, 1.1 mm height) have been characterized26 and used extensively for multiphoton microscopy experiments27,28,29,31,32,36.</li>
	</ol>
	</li>
	<li>Transducer reuse and coverslip replacement
	<ol>
		<li>Replace the coverslip if it is cracked or has debris (e.g., fur, glue) from the previous experiment. To remove the coverslip, dissolve the glue by submerging the transducer and coverslip in acetone for 20 min. 
		NOTE: Acetone may affect the integrity of the transducer and/or electrodes. Check with the manufacturer before proceeding with this step.</li>
		<li>Check if the acetone has dissolved the glue by gently pulling on the coverslip with forceps. Check once every 10 min to avoid prolonged acetone exposure.</li>
	</ol>
	</li>
</ol>
2. Animal preparation
<ol>
	<li>Anesthetize the animal by using a mix of medical air, oxygen, and isoflurane in an induction chamber. 
	NOTE: Use of oxygen as a carrier gas has been reported to affect the half-life of microbubbles37,38 and diminish the magnitude of ultrasound-microbubble induced increases in BBB permeability27, but may also reduce the risk of hypoxia and mortality39. Choose carrier gases based on project aims and veterinarian advice. Injectable anesthetics such as a ketamine/xylazine cocktail may also be used; however, it is easier to control the plane of anesthesia and blood oxygen levels when using inhalable anesthetics.</li>
	<li>Check that the animal has achieved a sufficient plane of anesthesia by performing a toe pinch. Weigh the animal to determine the dosage of dextran, microbubbles, and drugs to administer. Remove the fur from animal&#39;s head and place the animal onto a stereotactic frame.</li>
	<li>For acute experiments, access to the systemic circulation must be established for dextran and microbubble injections. To achieve this, insert a 27 g catheter into a tail vein. 
	NOTE: While retro-orbital injections are also possible, tail veins are recommended due to the limited working space in the head area during multiphoton imaging.</li>
	<li>Transfer the animal onto the stereotactic frame and switch the anesthesia to the nose cone. Maintain the animal&#39;s core temperature of 37 &#176;C using a heat source, such as a heating pad or a glove filled with warm water.</li>
	<li>Monitor animal temperature by using a rectal probe, and animal physiology by using a pulse oximeter. Apply ophthalmic ointment. Inject appropriate pre-surgery analgesic and/or anti-inflammatory drugs (see Table of Materials).</li>
	<li>Prior to starting the cranial window surgery, check the plane of anesthesia and the animal&#39;s heart rate, O2 saturation, respiratory rate, and temperature.</li>
	<li>To begin the cranial window surgery, remove the fur on the head by applying a depilatory cream and/or using fur clippers. Remove the fur from between the eyes to the anterior half of the neck (Figure 4A). 
	NOTE: Prolonged contact with the depilatory cream will burn the skin. For chronic cranial window surgeries, wash the scalp with alternating wipes of betadine and 70% EtOH following fur removal. Prepare the surgical space for sterile surgery. Sterility must be maintained until Step 2.15.</li>
	<li>To remove the scalp, lift the skin between the eyes using forceps held in the non-dominant hand, along the sagittal suture. Using curved scissors, remove the skin to expose the parietal bones (Figure 4B). Apply firm pressure with a cotton swab if there is bleeding from the skull or scalp; bleeding must be stopped before progressing to the next step. 
	NOTE: For acute surgeries, the skin can be pushed back and adhered to the skull using liquid cyanoacrylate glue or tissue adhesive.</li>
	<li>Remove the periosteum covering the outer surface of the skull using cotton swabs.</li>
	<li>Using an operating microscope (6-25x) and a dental drill (0.5 mm drill burr, medium speed), outline a circle onto the parietal bone to mark the desired location of the cranial window on the skull (Figure 5). Avoid the sagittal suture, lambda, and bregma, as these areas are thinner and overlay large blood vessels. 
	NOTE: To facilitate drilling, an outline of the cranial window can be drawn onto the skull using a marker and stencil (Figure 5A). For rats, it may be easier to drill a rectangular, instead of a circular, cranial window. Due to the thickness of the rat skull bone, use a 0.7 mm drill bit to outline the cranial window in the compact bone prior to using a 0.5 mm drill bit to complete the drilling process.</li>
	<li>Apply gentle pressure with the drill bit; excessive pressure increases the risk of causing damage to brain tissue. To prevent the skull from overheating during drilling, drip saline onto the skull using a syringe, or apply a piece of surgical sponge soaked in saline.</li>
	<li>Alternate between drilling and cooling the skull until the resulting bone island separates from the rest of the skull. Check the drilling progress by applying gentle pressure onto the bone island using forceps or the drill bit. Continue drilling until the bone island separates from the rest of the skull. 
	NOTE: Small cracks in the thinnest areas of the skull are a good indication that drilling is almost complete. Attempting to remove the bone island prematurely can cause pieces of bone to penetrate into the brain tissue, damaging the dura and causing inflammation and bleeding.</li>
	<li>Remove the bone island by using a pair of fine forceps to grasp the edges, or the upper compact bone layer, of the bone island (Figure 6A). Ensure that the brain is kept moist by applying a piece of surgical sponge that has been pre-soaked in saline. If bleeding is observed, place the surgical sponge on the region that is bleeding. Do not proceed to the next step until bleeding has ceased. 
	NOTE: If bleeding persists after 5 min, the animal cannot be used for multiphoton imaging experiments. For rats, it may be necessary to remove the dura if it is thick. To remove the dura, use high magnification on the operating microscope and a pair of fine forceps.</li>
	<li>To place a cranial window, pick up a glass coverslip with a pair of forceps, place a drop of saline onto one side, and maneuver it over the hole in the skull. Ensure that there are no air bubbles under the coverslip. 
	NOTE: Use a 5 mm glass coverslip for mice, and 8 mm for rats. For rats, due to the thickness of the skull bone, use an agarose solution instead of saline to fill in the space between the coverslip and brain. The transducer and its coverslip can also be adhered directly onto the skull, instead of using a separate coverslip for the cranial window. For this option, proceed to step 3.1. Refer to Figure 1 for details.</li>
	<li>Spread a layer of cyanoacrylate glue around the perimeter of the coverslip (Figure 6B) to attach it to the skull. Ensure that there is no glue under the coverslip. Apply pressure onto the coverslip to ensure that glue does not come into contact with the brain.</li>
	<li>Once the glue is completely dry, even out the surface of the glue by using the dental drill. Ensure all glue debris is removed from the surgical area. 
	&#8203;NOTE: For chronic cranial windows, inject the necessary post-surgical drugs (see Table of Materials), provide ointment for wound care and soft foods, and recover the animal under a heat lamp.</li>
</ol>
3. Placement of the ring transducer
<ol>
	<li>Prepare the 1% (w/v) agarose solution. In a small beaker or Erlenmeyer flask, add 0.1 g of agarose and 10 mL of PBS (1x) or saline. Boil the solution until the agarose has fully dissolved by placing the beaker onto a hotplate or heating the solution in a microwave oven (30-45 s).</li>
	<li>Steps 3.2-3.5 are time-sensitive as the agarose solution cools quickly. Withdraw ~ 0.5 mL of agarose into a 1 mL syringe. 
	NOTE: To protect the integrity of the brain, ensure that the temperature of the agarose approximates body temperature before use.</li>
	<li>Deposit the agarose liberally onto the coverslip of the cranial window. 
	NOTE: If the tissue blanches, the temperature of the agarose was too high; the animal must be euthanized. If there is no separate coverslip covering the brain (i.e., the transducer and its coverslip are placed directly onto the brain, see step 2.14), then agarose should be deposited onto the surface of the brain in this step.</li>
	<li>Place the transducer over the cranial window (Figure 6C). Apply firm pressure such that there is minimal agarose between the transducer and the cranial window. Ensure that the transducer is centered (XY-plane) and parallel (Z-plane) to the cranial window, and that there are no air bubbles in the agarose.</li>
	<li>When the agarose has cooled to a jello-like consistency, cut away excess agarose from the circumference of the transducer&#39;s coverslip using a spatula or scalpel. Ensure that there are no air bubbles underneath the transducer&#39;s coverslip.</li>
	<li>Using a spatula, spread a layer of cyanoacrylate glue over the circumference of the transducer&#39;s coverslip, extending to the skull, such that the transducer is firmly adhered to the skull.</li>
	<li>Maintain firm pressure on the transducer until the glue has completely dried (10-15 min).</li>
</ol>
4. Multiphoton microscopy imaging
<ol>
	<li>Position the animal under the objective lens (Figure 7A). Ensure that the objective lens is centered in the ring transducer, and parallel with the transducer (Figure 7B). If a water-immersion objective lens is used, fill the center of the ring transducer with deionized and degassed water. 
	NOTE: Degassed water is important for proper ultrasound propagation.</li>
	<li>Start with the objective lens in its highest position, and then slowly lower the objective lens until it is within the ring transducer (Figure 7A, B). Ensure that objective lens does not collide with the transducer or coverslip. 
	NOTE: Alternate between the eyepiece to check if the Z-position of the objective lens is in-plane with the surface of the brain, and by eye to ensure that the objective lens does not collide with the transducer or coverslip. It may be easier to visualize the pial vessels through the eyepiece following injection of fluorescent dextran through the tail vein (Figure 7C).</li>
	<li>Prepare the multiphoton microscope for imaging. 
	NOTE: This protocol uses an upright multiphoton microscope and a 20-25x objective lens that has a working distance of 2 mm, which is sufficient to focus beyond the coverslip(s), into the brain parenchyma.</li>
	<li>Prepare the dextran. Add the appropriate amount of PBS to the vial of dextran, as per the manufacturer&#39;s instructions. Vortex the dextran solution for 1-3 min to ensure that the dextran powder is fully dissolved. Inject the dextran solution into the tail vein.</li>
	<li>Setting up an image scan
	<ol>
		<li>Using the eyepieces, ensure that the objective lens is parallel to the brain. Tilt the animal to correct for XZ and YZ misalignments.</li>
		<li>Select a field-of-view in a multiphoton microscope. Set up an XYZ scan before ultrasound exposure to have a baseline image of the vasculature prior to ultrasound exposure. 
		&#8203;NOTE: Typical imaging parameters are as follows: 300-800 &#181;m in depth, 2-5 &#181;m step-size, and 10-20 time stacks. Ensure that the objective lens does not come into contact with the transducer or coverslip at its lowest point during the imaging sequence.</li>
	</ol>
	</li>
</ol>
5. Ultrasound exposure
<ol>
	<li>Ensure all the BNC cables are connected correctly (Figure 3).</li>
	<li>Set up an XYZT image scan that is sufficiently long enough to capture image stacks before, during, and after ultrasound-microbubble treatments.</li>
	<li>Prepare the microbubbles by following the manufacturer&#39;s instructions. Inject the microbubbles into the tail vein and begin imaging. 
	NOTE: Microbubble injections can be done with an infusion pump to ensure consistent injection rate and to enable concurrent microbubble injection and imaging. If microbubbles are to be injected during imaging, ensure that the tail vein can be easily accessed without exposing the detectors to ambient light.</li>
	<li>Begin sonication. 
	NOTE: Typical sonication parameters are as follows: 10 ms cycles, mechanical index of 0.2-0.4, and pulse repetition frequencies between 1-4 Hz. Sonication and microbubble parameters used in preclinical ultrasound-microbubble studies have been extensively studied and are well documented in literature (e.g. see 40 for a review).</li>
	<li>Continue multiphoton imaging throughout the duration of sonication and following the end of sonication. Be observant for dextran extravasation from blood vessels, as this is indicative of increases in BBB permeability. 
	NOTE: If dextran is detected in the extravascular space, but in the periphery of the field-of-view, then there may be affected blood vessels outside of the field-of-view. This can result from misalignment of the transducer with the focus of the objective lens. In this scenario, it is easier to adjust the field-of-view by moving the objective lens or by repositioning the animal, than to realign the transducer.</li>
	<li>Once imaging is completed, euthanize the animal cervical dislocation under deep anesthesia or CO2 asphyxiation. For chronic cranial windows, spread a layer of dental cement onto the exposed skull. 
	&#8203;NOTE: For chronic cranial windows, the skin surrounding the window can be sutured, although this is not necessary, due to the removal of the scalp in step 2.8.</li>
</ol>
6. Image analysis
<ol>
	<li>Export image stacks.</li>
	<li>Analyze images with image analysis software (e.g., Olympus Fluoview, ImageJ/FIJI, Bitplane Imaris, ThermoFisher Scientific Amira) and/or programming tools (e.g., Python, MATLAB).</li>
</ol>

Charissa Poon, Melina M&#252;hlenpfordt, Marieke Olsman, and Catharina de Lange Davies declare no financial nor non-financial competing conflicts of interest. Spiros Kotopoulis is a full-time employee and owns shares in EXACT Therapeutics AS, a company developing ultrasound and microbubble/cluster enhanced drug delivery. Kullervo Hynynen is the founder of FUS Instruments, from which he receives non-research related support.

Intravital multiphoton microscopy monitoring of the brain is a valuable tool to study brain responses during ultrasound exposure. To our knowledge, the protocol described here is the only method of conducting multiphoton microscopy imaging of the brain parenchyma during ultrasound-microbubble treatments. The creation of cranial windows and the use of ring transducers allow real-time monitoring of vascular, cellular, and other downstream responses to ultrasound-microbubble treatments at high spatial and temporal resolution. Other groups have performed multiphoton microscopy imaging following the completion of ultrasound-microbubble treatments, thereby missing the real-time response of the brain parenchyma to treatments19. The procedure described offers improved temporal control, allowing the collection of data that may help illuminate the acute mechanisms behind ultrasound-microbubble treatments. Quantitative and qualitative data can be extracted and analyzed from the acquired image stacks, such as extravasation kinetics27,29,30, changes in &#946;-amyloid plaque volume31, and cell dynamics32.
Several troubleshooting steps were highlighted throughout the protocol. First, surgical steps that are particularly susceptible to operator error were emphasized, such as use of agarose during cranial window surgery and placement of the transducer. Steps to prevent animal discomfort and death were also provided, including monitoring animal physiology during surgery, and thoroughly vortexing the dextran prior to injection. Second, physical specifications of the transducer, and alignment of the objective lens, transducer, and cranial window, were also highlighted. The specifications of the ring transducer and its acoustic properties must be determined in consideration of the objective lens used as well as the animal model. Specifically, the inner diameter of the ring transducer must be large enough to surround the objective lens, but small enough to be mounted securely onto the animal&#39;s skull. In addition, the focal area of the transducer must align with the range of the objective lens used.
A common challenge is that the cranial window and ring transducer are angled relative to the objective lens. Proper centering (XY) and alignment (Z) of the objective lens with the cranial window and transducer ensures that the focal area of the transducer, and thus the region of treated brain tissue, aligns with the imaging field-of-view, and reduces the risk of collision between the objective lens and transducer during imaging. Alignment can be achieved by adjusting the head position of the animal and/or by rotating the stereotactic frame that it is fixed in.
Microscope components (e.g., detectors, beam splitters) and image acquisition parameters should be selected based on the aim of the study. Here, an objective lens with a long focal length (&#62; 2 mm) is used due to the presence of the coverslip(s) and ring transducer located between the objective lens and the brain. An upright microscope is also recommended as it allows for more space to maneuver the animal, particularly for brain experiments. To capture the kinetics of ultrasound-microbubble induced leakage of the intravascular dye, a high temporal resolution is favorable, which can be achieved by using a resonance scanning system. Combining this with a high sensitivity detection system, such as gallium arsenide phosphide (GaAsP) detectors, will also result in more favorable images.
The experimental procedure presented has several limitations. First, the surgical procedure is quite invasive, and has been reported to cause inflammation45, although inflammation can be minimized46. Moreover, immune responses induced by cranial window surgeries were observed to resolve by 2-4 weeks following surgery23,24,25. In addition, the drilling process, particularly when conducted with excessive force or speed, can cause damage to underlying tissue due to the generation of heat, vibration, and pressure applied. Cranial window surgeries and multiphoton imaging have also been observed to affect brain temperature47. These limitations can be reduced to an extent through careful creation of pristine cranial windows, proper recovery of animals with chronic cranial windows, and maintenance of normothermic body temperature using a heating source with feedback control. Second, the imaging depth is limited by the microscope and objective lens used. For example, the effect of ultrasound-microbubble treatment in deeper brain structures, such as the hippocampus, cannot be studied without more invasive measures, such as the removal of overlying cortical tissue48, or the use of microlenses in conjunction with cortical penetration49. Using an objective lens with a long working distance could resolve this issue to an extent, but light penetration is also limited at greater depths.
While the representative images of this protocol were acquired from wild-type rodents, the presented experimental procedure can also be applied to transgenic animals and disease models, such as Alzheimer&#39;s disease31. Ultrasound experiments unrelated to BBB modulation, such as ultrasound-induced neuromodulation, can also be monitored using this protocol33,34. Other possible applications can be achieved by using different microscope or detector set-ups, such as pairing a confocal microscope with an ultra-high-speed camera50. While photobleaching and phototoxicity are comparatively worse in confocal microscopes due to the large excitation volume, ultra-high-speed imaging may enable visualization of brain capillary endothelial cell-microbubble interactions with high temporal resolution, which could further illuminate the mechanisms driving ultrasound-microbubble BBB treatments. To conclude, the protocol described provides a method to monitor vascular and cellular effects induced by ultrasound-microbubble BBB experiments in real-time, providing a tool to further determine the mechanisms driving these treatments, as well as illuminating the downstream responses of the brain parenchyma to ultrasound-microbubble treatments.

A key challenge to treating neurological disorders is the presence of the blood-brain barrier (BBB). The BBB limits hydrophilic, charged, polar, and large (&#62; 400 Da) molecules from entering the brain parenchyma1. One method currently used to deliver therapeutics across the BBB into the brain parenchyma is to use stereotactic intracranial injections2. Other less invasive methods under investigation are hindered by the complexity of the techniques used, such as designing drugs for receptor-mediated delivery across the BBB3, or are limited in the spatial precision of targeted areas, such as intranasal injections4 or administration of hyperosmotic solutions5.
The use of ultrasound in conjunction with systemically injected microbubbles, an ultrasound contrast agent, has been developed as a noninvasive means to transiently increase the permeability of the BBB6. By using a focused transducer7 or a steerable phased array of transducers8,9, ultrasound can be targeted to selected areas in the brain with millimeter level precision, minimizing off-target effects. Ultrasound-microbubble treatments can be customized to each subject&#39;s brain anatomy by using magnetic resonance imaging guidance7,10,11,12,13,14 or stereotactic frames15. Furthermore, the extent of increase in BBB permeability can be controlled in real-time by monitoring acoustic emissions from microbubbles16,17,18. Clinical trials investigating the safety and feasibility of ultrasound-microbubble treatments are currently in progress worldwide (e.g., ClinicalTrials.gov identifier NCT04118764).
Ultrasound-microbubble BBB treatments are typically evaluated by confirming treatment induced increases in BBB permeability, visualized in contrast-enhanced magnetic resonance imaging, or by dye extravasation in in vivo imaging or ex vivo histology. However, most microscopic analyses have been performed ex vivo, following the completion of ultrasound-microbubble treatments11,19, thereby missing the dynamic biological responses during, and immediately following, ultrasound exposure. Real-time imaging conducted during ultrasound exposure may aid in understanding the mechanisms driving ultrasound-microbubble BBB treatments as well as downstream responses, which may increase our understanding of its therapeutic applications. Furthermore, the use of chronic cranial windows with in vivo imaging techniques would enable longitudinal studies to evaluate temporal aspects of ultrasound-microbubble treatments.
The goal of this protocol is to describe the surgical and technical procedures required to conduct real-time multiphoton imaging of ultrasound-microbubble treatments for acute and chronic studies in rodents (Figure 1). This is achieved in two parts: first, to create a cranial window to enable in vivo imaging, and second, to mount a ring transducer on the top to enable concurrent sonication and imaging. Cranial windows have been extensively used by neuroscientists for in vivo imaging of neurovascular coupling20, &#946;-amyloid pathogenesis21, and neuroimmunology22, among others. In this protocol, surgical procedures for creating acute (non-recovery) and chronic (recovery) cranial windows in the mouse and rat skull are described. Cranial window methodologies, particularly for chronic experiments, have been well-documented23,24,25. To be consistent with existing literature, the terms &#39;acute&#39; and &#39;chronic&#39; will be used throughout this protocol. The design of ring transducers for in vivo imaging has also been previously described26. Despite the availability of these techniques and the insights that can be gained from real-time imaging of ultrasound-microbubble treatments, there are very few research laboratories that have successfully published literature using this technique26,27,28,29,30,31,32. As such, in this protocol, the surgical and technical details of conducting these real-time ultrasound-microbubble experiments are described. While the specified sonication and imaging parameters have been optimized for BBB experiments, other effects of ultrasound exposure to the brain, such as neuromodulation33,34, &#946;-amyloid plaque monitoring31, and immune cell responses32, can also be investigated using this technique.

<table><tbody><tr><td>&lt;strong&gt;Ring transducer placement&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Agarose (powder)</td><td>Sigma-Aldrich</td><td>A9539</td><td></td></tr><tr><td>Beaker or Erlenmeyer flask (50 ml)</td><td>VWR</td><td>213-0462 or 214-1130</td><td></td></tr><tr><td>Cyanoacrylate glue (gel)</td><td>Loctite</td><td>1363589</td><td></td></tr><tr><td>Glass coverslips (13 mm)</td><td>Thermo Fisher Scientific</td><td>CB00130RA120MNT0</td><td>Coverslip for ring transducer.</td></tr><tr><td>Hot plate or microwave</td><td>Corning</td><td>PC-400D</td><td>To heat agarose solution.</td></tr><tr><td>PBS (1X)</td><td>Sigma-Aldrich</td><td>P4417</td><td></td></tr><tr><td>Ring transducer</td><td>Custom-made</td><td>Custom-made</td><td>Custom-made. E.g. https://doi.org/10.1109/ULTSYM.2014.0518</td></tr><tr><td>Rubber stopper</td><td>VWR</td><td>217-0867</td><td></td></tr><tr><td>&lt;strong&gt;Animal preparation and drugs&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Bupivacaine*&lt;sup&gt;A&lt;/sup&gt;</td><td>Aspen</td><td>169912</td><td>Dose: 1 mg/kg, s.c., local anesthetic injected at incision site.</td></tr><tr><td>Buprenorphine*&lt;sup&gt;A&lt;/sup&gt;</td><td>Indivior</td><td>521634</td><td>Dose mouse: 0.05-0.1 mg/kg, s.c., opioid, administer pre-surgery.</td></tr><tr><td>Buprenorphine*&lt;sup&gt;A&lt;/sup&gt;</td><td>Indivior</td><td>521634</td><td>Dose rat: 0.01-0.05 mg/kg, s.c..</td></tr><tr><td>Carprofen*&lt;sup&gt;C&lt;/sup&gt;</td><td>Pfizer</td><td>DIN 02255693</td><td>Dose: 5 mg/kg, s.c., NSAID, adminster post-surgery.</td></tr><tr><td>Depilatory cream</td><td>Veet</td><td>N/A</td><td>For complete fur removal after trimming.</td></tr><tr><td>Dexamethasone*&lt;sup&gt;C&lt;/sup&gt;</td><td>Sandoz</td><td>DIN 00664227, 2301</td><td>Dose: 3 mg/kg, i.m., corticosteroid, reduces cerebral edema, administer pre-surgery.</td></tr><tr><td>Enrofloxacin*&lt;sup&gt;C&lt;/sup&gt;</td><td>Bayer</td><td>DIN: 02249243</td><td>Dose: 5 mg/kg, i.p., antibiotic, administer post-surgery.</td></tr><tr><td>Fur clippers</td><td>Aesculap</td><td>90200714</td><td>Exacta/Isis.</td></tr><tr><td>Heating pad</td><td>Physitemp Instruments INC</td><td>HP-1M</td><td></td></tr><tr><td>Isoflurane</td><td>Baxter</td><td>ESDG9623C</td><td>Dose: 3% induction, 1% maintenance; anesthetic.</td></tr><tr><td>Meloxicam*&lt;sup&gt;A&lt;/sup&gt;</td><td>Boehringer Ingelheim Vetmedica GmbH</td><td>25388</td><td>Dose mouse: 2-3 mg/kg, s.c., NSAID, administer pre-surgery.</td></tr><tr><td>Meloxicam*&lt;sup&gt;A&lt;/sup&gt;</td><td>Boehringer Ingelheim Vetmedica GmbH</td><td>25388</td><td>Dose rat: 1 mg/kg, s.c.</td></tr><tr><td>Pulse oximeter</td><td>STARR Life Sciences Corp</td><td>N/A</td><td>MouseOx.</td></tr><tr><td>Stereotaxic frame</td><td>Kopf</td><td>Kopf 900</td><td></td></tr><tr><td>Sterile ophthalmic ointment</td><td>Th&amp;eacute;a</td><td>597562</td><td>Viscotears.</td></tr><tr><td>Tail vein catheter (24 G)</td><td>BD Neoflon</td><td>391350</td><td></td></tr><tr><td>* Discuss dosing and type of administration with veterinarian prior to use. &lt;sup&gt;A &lt;/sup&gt;For acute window surgeries, &lt;sup&gt;C&lt;/sup&gt; For chronic window surgeries. Dose for mice and rats are the same unless otherwise specified.</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Material and equipment for cranial window placement&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Alcohol swabs</td><td>BD</td><td>326895</td><td></td></tr><tr><td>Curved fine surgical scissors</td><td>Fine Science Tools</td><td>14002-12</td><td></td></tr><tr><td>Cotton or fibreless swabs</td><td>Chemtronics</td><td>CX50</td><td></td></tr><tr><td>Cyanoacrylate glue (gel)</td><td>Loctite</td><td>1594457 (gel), 230992 (liquid)</td><td>If unavailable, liquid cyanoacrylate glue can be mixed with extra-fine acrylate powder.</td></tr><tr><td>Dental cement</td><td>Lang Dental</td><td>Jet Set-4 Denture Repair Package</td><td></td></tr><tr><td>Dental micromotor hand drill</td><td>FOREDOM</td><td>K.1070-2</td><td>High speed rotary micromotor kit with 2.35 mm collet.</td></tr><tr><td>Forceps</td><td>Fine Science Tools</td><td>11152-10, 11370-40</td><td></td></tr><tr><td>Glass coverslips</td><td>Thermo Fisher Scientific</td><td>CB00050RA120MNT0 (5 mm)</td><td>Mouse cranial windows.</td></tr><tr><td>Glass coverslips</td><td>Thermo Fisher Scientific</td><td>CB00080RA120MNT0 (8 mm)</td><td>Rat cranial windows.</td></tr><tr><td>Micro drill burrs (0.5 mm)</td><td>Meisinger</td><td>HM71005 (0.5 mm)</td><td></td></tr><tr><td>Micro drill burrs (0.7 mm)</td><td>Meisinger</td><td>HM71007 (0.7 mm)</td><td></td></tr><tr><td>Stereo microscope</td><td>Nikon</td><td>SMZ645</td><td></td></tr><tr><td>Surgical gelatin sponge</td><td>Ethicon</td><td>MS0005</td><td></td></tr><tr><td>Vetbond Tissue adhesive</td><td>3M</td><td>1469SB</td><td></td></tr><tr><td>Weigh boats / trays</td><td>VWR</td><td>10803-148</td><td></td></tr><tr><td>* Autoclave drapes, tools, materials, and gowns, and use sterile surgical gloves, for chronic cranial window surgeries.</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Multiphoton microscopy&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>20x water immersion objective</td><td>Olympus</td><td>XLUMPLFLN20 XW</td><td>Numerical aperture 1.0, working distance 2.0 mm.</td></tr><tr><td>Fluorescent dextran (e.g. FITC 70 kDa)</td><td>Sigma Aldrich</td><td>46945</td><td>Recommended 10 kDa-2 MDa.</td></tr><tr><td>MaiTai DeepSee Ti:Sapphire laser oscillator</td><td>Spectra-Physics</td><td>N/A</td><td></td></tr><tr><td>SliceScope microscope</td><td>Scientifica</td><td>N/A</td><td></td></tr><tr><td>&lt;strong&gt;Ultrasound treatment&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>50 dB RF Amplifier</td><td>E&amp;amp;I</td><td>2100L</td><td></td></tr><tr><td>Matching circuit</td><td>Custom-made</td><td>Custom-made</td><td>Custom-made.</td></tr><tr><td>Microbubbles</td><td>Bracco Imaging</td><td>N/A</td><td>SonoVue (Bracco Imaging, Europe). Dose 1 ml/kg.</td></tr><tr><td>Microbubbles</td><td>Lantheus</td><td>N/A</td><td>Definity (Lantheus Medical Imaging, North America). Dose 0.02-0.04 ml/kg.</td></tr><tr><td>Signal generator</td><td>Agilent Technologies</td><td>33500B</td><td></td></tr></tbody></table>

real-time intravital multiphoton microscopy to visualize focused ultrasound and microbubble treatments to increase blood-brain barrier permeability

The blood-brain barrier (BBB) is a key challenge for the successful delivery of drugs to the brain. Ultrasound exposure in the presence of microbubbles has emerged as an effective method to transiently and locally increase the permeability of the BBB, facilitating para- and transcellular transport of drugs across the BBB. Imaging the vasculature during ultrasound-microbubble treatment will provide valuable and novel insights on the mechanisms and dynamics of ultrasound-microbubble treatments in the brain.
Here, we present an experimental procedure for intravital multiphoton microscopy using a cranial window aligned with a ring transducer and a 20x objective lens. This set-up enables high spatial and temporal resolution imaging of the brain during ultrasound-microbubble treatments. Optical access to the brain is obtained via an open-skull cranial window. Briefly, a 3-4 mm diameter piece of the skull is removed, and the exposed area of the brain is sealed with a glass coverslip. A 0.82 MHz ring transducer, which is attached to a second glass coverslip, is mounted on top. Agarose (1% w/v) is used between the coverslip of the transducer and the coverslip covering the cranial window to prevent air bubbles, which impede ultrasound propagation. When sterile surgery procedures and anti-inflammatory measures are taken, ultrasound-microbubble treatments and imaging sessions can be performed repeatedly over several weeks. Fluorescent dextran conjugates are injected intravenously to visualize the vasculature and quantify ultrasound-microbubble induced effects (e.g., leakage kinetics, vascular changes). This paper describes the cranial window placement, ring transducer placement, imaging procedure, common troubleshooting steps, as well as advantages and limitations of the method.

Successful ultrasound-microbubble treatments can be detected by the extravasation of fluorescent dextran from the intravascular to the extravascular space (Figure 8), indicating an increase in BBB permeability. Depending on the pressure field of the ring transducer, pial vessels and/or capillaries will be affected.
To evaluate the vascular changes induced by ultrasound-microbubble treatments, the diameter of the vessel of interest can be measured before, during, and after ultrasound-microbubble treatment (Figure 9). This can be done manually in a commercially available software (e.g., Olympus Fluoview software). During image acquisition, bolus dextran injections and line scans can also be used to assess blood flow30,41. To evaluate kinetics of dextran leakage as a representative model for drug delivery, the signal intensity between the intra- and extravascular spaces can be evaluated using tools such as MATLAB26,27,29,41 (Figure 10).
Further image processing can be achieved using ImageJ/FIJI. ImageJ/FIJI is an open-source software that is compatible with MATLAB and is well-suited to conduct common analyses in biological image analysis, such as measuring vascular changes, or the lengths of or distance between fluorescent objects (e.g., &#946;-amyloid plaques to blood vessels). Image processing pipelines created in ImageJ/FIJI can be automated by writing custom macros.
More complex analyses, such as 3D segmentation of blood vessels and cell tracking, can be achieved using more advanced, semi-automated software (Figure 11). Following segmentation, more specific analyses can be conducted, such as classifying blood vessels as arterioles, venules, or capillaries, based on diameter, branching, tortuosity patterns, and flow direction42,43. Machine learning algorithms have also been developed to automate blood vessel segmentation22,44.
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/62235/62235fig1v4.jpg" /> 
Figure 1: General workflow of intravital multiphoton ultrasound-microbubble brain experiments. A general workflow of the intravital multiphoton ultrasound-microbubble brain experiments described in this protocol is shown. There are 6 steps: (A) Animal preparation for (A1) mice and (A2) rats, (B) Dextran injection, (C) Microbubble injection, (D) Pre-treatment imaging, (E) Treatment and imaging, (F) Post-treatment imaging and data analysis. <a href="https://www.jove.com/files/ftp_upload/62235/62235fig1v4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/62235/632235fig02.jpg" /> 
Figure 2: Cross-section and top view of 3D-printed mold. (A) Cross-section of the mold. A thin layer of cyanoacrylate glue is applied on the top surface of the ring transducer, and a coverslip is placed on top. A stamp may be used to apply firm, even pressure on the coverslip and ring transducer. (B) Top view of the mold. A notch can be added in the mold to facilitate removal of the prepared transducer. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig02large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/62235/632235fig03.jpg" /> 
Figure 3: Ultrasound set-up. Typical hardware for ultrasound experiments are shown. Ultrasound parameters are set and triggered by the signal generator and amplified by the amplifier. A power meter can be used to record forward and reflected powers prior to sending the signal to the matching box, which is matched to the transducer. All connections are achieved using BNC cables unless stated otherwise. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig03large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/62235/632235fig04.jpg" /> 
Figure 4: Area of fur removal and scalp removal. (A) Fur removal should start from between the eyes and extend until the anterior half of the neck. (B) Scalp removal should be sufficient to expose the parietal bones. Bleeding must be stopped before proceeding. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig04large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" class="xfigimg" src="/files/ftp_upload/62235/632235fig05.jpg" /> 
Figure 5: Outline of the cranial window. The cranial window is situated on a parietal bone. (A) An outline of the cranial window can be drawn onto the skull to aid in the drilling process. (B) The outline of the cranial window can be seen following drilling through the compact bone. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig05large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 6" class="xfigimg" src="/files/ftp_upload/62235/632235fig06.jpg" /> 
Figure 6: Cranial window and transducer alignment. (A) The cranial window is created on a parietal bone. The bone island has been removed, exposing the brain underneath. (B) The cranial window is complete when a glass coverslip is sealed onto the skull using cyanoacrylate glue. (C) The transducer is centered to the cranial window and adhered using cyanoacrylate glue. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig06large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 7" class="xfigimg" src="/files/ftp_upload/62235/632235fig07.jpg" /> 
Figure 7: Positioning of objective lens and transducer. (A,B) The objective lens is centered to the ring transducer. (C) Blood vessels filled with fluorescent dextran are visible through the eyepieces, under epifluorescence. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig07large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 8" class="xfigimg" src="/files/ftp_upload/62235/632235fig08.jpg" /> 
Figure 8: Maximum projection multiphoton images of ultrasound-microbubble induced increases in BBB permeability. Maximum projection images of vasculature (A) before and (B) after ultrasound-microbubble treatments. Successful ultrasound-microbubble treatments can be confirmed by observing increases in BBB permeability following treatment, visualized as fluorescent dextran extravasation (arrows). Scale bar: 50 &#181;m. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig08large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 9" class="xfigimg" src="/files/ftp_upload/62235/62235fig9v4.jpg" /> 
Figure 9: Analysis of vasomodulation induced by ultrasound-microbubble treatments. Maximum projection images of cerebral blood vessels before, during, and after ultrasound-microbubble treatments. Microbubbles are present in all images. Compared to (A) pre-treatment conditions, clear vasomodulation can be observed (B) during ultrasound-microbubble treatments (red arrows). Ultrasound-microbubble mediated increases in BBB permeability are also evident following treatment from the leakage of fluorescent dextran from the intravascular to the extravascular space (yellow arrows). (C) When ultrasound is turned off, vascular diameters return to pre-treatment, baseline sizes. (D) Vascular changes can be analyzed by plotting the diameter of the vessel of interest before, during, and after ultrasound-microbubble treatment. Scale bar: 100 &#181;m. (Unpublished work). <a href="https://www.jove.com/files/ftp_upload/62235/62235fig9v4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 10" class="xfigimg" src="/files/ftp_upload/62235/62235fig10v4.jpg" /> 
Figure 10: Analysis of leakage kinetics following ultrasound-microbubble treatments. Increase in BBB permeability is visualized as leakage of fluorescent dextran from the intravascular to the extravascular space. Changes in BBB permeability are evident when comparing image stacks acquired (A) before and (B) after ultrasound-microbubble treatments. (C) Leakage kinetics can be analyzed by tracking the intensity, volume, and speed of dextran in extravascular compartments (yellow rectangle). Scale bar: 50 &#181;m. (Unpublished work.) <a href="https://www.jove.com/files/ftp_upload/62235/62235fig10v4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 11" class="xfigimg" src="/files/ftp_upload/62235/632235fig11.jpg" /> 
Figure 11: Blood vessel segmentation of multiphoton microscopy XYZ stack. (A) Depth (XYZ) stack of blood vessels in a transgenic EGFP rat. Blood vessels are visualized via intravenous injection of fluorescent Texas Red 70 kDa dextran (red). The green channel shows fluorescent cells and tissue autofluorescence. (B) 3D reconstructions of blood vessels are created, and then color-coded according to blood vessel type to facilitate type-specific analyses. Vein/venules are blue, arteries/arterioles are red, and capillaries are cyan. Scale bar: 50 &#181;m. Reconstructions created using Bitplane Imaris. <a href="https://www.jove.com/files/ftp_upload/62235/632235fig11large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>

Watch this Scientific Journal Video about Real-Time Intravital Multiphoton Microscopy to Visualize Focused Ultrasound and Microbubble Treatments to Increase Blood-Brain Barrier Permeability at JoVE.co

Real-Time Intravital Multiphoton Microscopy to Visualize Focused Ultrasound and Microbubble Treatments to Increase Blood-Brain Barrier Permeability

This protocol describes the surgical and technical procedures that enable real-time in vivo multiphoton fluorescence imaging of the rodent brain during focused ultrasound and microbubble treatments to increase blood-brain barrier permeability.

The blood-brain barrier (BBB) is a key challenge for the successful delivery of drugs to the brain. Ultrasound exposure in the presence of microbubbles ...

real-time-intravital-multiphoton-microscopy-to-visualize-focused

Research

JoVE Journal

Bioengineering

4.3K Views.  Sunnybrook Research Institute. Echografieblootstelling in de aanwezigheid van microbubbels is naar voren gekomen als een effectieve methode om de permeabiliteit van de bloed-hersenbarrière tijdelijk en lokaal te verhogen. Normaal gesproken belemmert de bloed-hersenbarrière de levering van potentiële geneesmiddelen voor verschillende hersenziekten. Na ultrasoonapparaat beginnen de geïnjecteerde microbubbels te oscilleren en veroorzaken ze spanning op de vaatwand, waardoor tight junctions worden geopend en uiteindelijk g...

Video: Real-Time Intravital Multiphoton Microscopy to Visualize Focused Ultrasound and Microbubble Treatments to Increase Blood-Brain Barrier Permeability

Contrast Ultrasound Targeted Treatment of Gliomas in Mice via Drug-Bearing Nanoparticle Delivery and Microvascular Ablation

We are developing minimally-invasive contrast agent microbubble based therapeutic approaches in which the permeabilization and/or ablation of the microvasculature are controlled by varying ultrasound pulsing parameters.  Specifically, we are testing whether such approaches may be used to treat malignant brain tumors through drug delivery and microvascular ablation.  Preliminary studies have been performed to determine whether targeted drug-bearing nanoparticle delivery can be facilitated by the ultrasound mediated destruction of "composite" delivery agents comprised of 100nm poly(lactide-co-glycolide) (PLAGA) nanoparticles that are adhered to albumin shelled microbubbles. We denote these agents as microbubble-nanoparticle composite agents (MNCAs). When targeted to subcutaneous C6 gliomas with ultrasound, we observed an immediate 4.6-fold increase in nanoparticle delivery in MNCA treated tumors over tumors treated with microbubbles co-administered with nanoparticles and a 8.5 fold increase over non-treated tumors. Furthermore, in many cancer applications, we believe it may be desirable to perform targeted drug delivery in conjunction with ablation of the tumor microcirculation, which will lead to tumor hypoxia and apoptosis. To this end, we have tested the efficacy of non-theramal cavitation-induced microvascular ablation, showing that this approach elicits tumor perfusion reduction, apoptosis, significant growth inhibition, and necrosis. Taken together, these results indicate that our ultrasound-targeted approach has the potential to increase therapeutic efficiency by creating tumor necrosis through microvascular ablation and/or simultaneously enhancing the drug payload in gliomas.

Insonation of microbubbles is a promising strategy for tumor ablation at reduced time-averaged acoustic powers, as well as for the targeted delivery of therapeutics. The purpose of the present study is to develop low duty cycle ultrasound pulsing strategies and nanocarriers to maximize non-thermal microvascular ablation and payload delivery to subcutaneous C6 gliomas.

We are developing minimally-invasive contrast agent microbubble based therapeutic approaches in which the permeabilization and/or ablation of the ...

MRI-guided Disruption of the Blood-brain Barrier using Transcranial Focused Ultrasound in a Rat Model

Focused ultrasound (FUS) disruption of the blood-brain barrier (BBB) is an increasingly investigated technique for circumventing the BBB1-5. The BBB is a significant obstacle to pharmaceutical treatments of brain disorders as it limits the passage of molecules from the vasculature into the brain tissue to molecules less than approximately 500 Da in size6. FUS induced BBB disruption (BBBD) is temporary and reversible4 and has an advantage over chemical means of inducing BBBD by being highly localized. FUS induced BBBD provides a means for investigating the effects of a wide range of therapeutic agents on the brain, which would not otherwise be deliverable to the tissue in sufficient concentration. While a wide range of ultrasound parameters have proven successful at disrupting the BBB2,5,7, there are several critical steps in the experimental procedure to ensure successful disruption with accurate targeting. This protocol outlines how to achieve MRI-guided FUS induced BBBD in a rat model, with a focus on the critical animal preparation and microbubble handling steps of the experiment.

Microbubble-mediated focused ultrasound disruption of the blood-brain barrier (BBB) is a promising technique for non-invasive targeted drug delivery in the brain1-3. This protocol outlines the experimental procedure for MRI-guided transcranial BBB disruption in a rat model.

Focused ultrasound (FUS) disruption of the blood-brain barrier (BBB) is an increasingly investigated technique for circumventing the BBB1-5. The BBB is a ...

Medicine

Multiplexing Focused Ultrasound Stimulation with Fluorescence Microscopy

By focusing low-intensity ultrasound pulses that penetrate soft tissues, LIPUS represents a promising biomedical technology to remotely and safely manipulate neural firing, hormonal secretion and genetically-reprogrammed cells. However, the translation of this technology for medical applications is currently hampered by a lack of biophysical mechanisms by which targeted tissues sense and respond to LIPUS. A suitable approach to identify these mechanisms would be to use optical biosensors in combination with LIPUS to determine underlying signaling pathways. However, implementing LIPUS to a fluorescence microscope may introduce undesired mechanical artefacts due to the presence of physical interfaces that reflect, absorb and refract acoustic waves. This article presents a step-by-step procedure to incorporate LIPUS to commercially-available upright epi-fluorescence microscopes while minimizing the influence of physical interfaces along the acoustic path. A simple procedure is described to operate a single-element ultrasound transducer and to bring the focal zone of the transducer into the objective focal point. The use of LIPUS is illustrated with an example of LIPUS-induced calcium transients in cultured human glioblastoma cells measured using calcium imaging.

Low-Intensity Pulsed Ultrasound Stimulation (LIPUS) is a modality for non-invasive mechanical stimulation of endogenous or engineered cells with high spatial and temporal resolution. This article describes how to implement LIPUS to an epi-fluorescence microscope and how to minimize acoustic impedance mismatch along the ultrasound path to prevent unwanted mechanical artefacts.

By focusing low-intensity ultrasound pulses that penetrate soft tissues, LIPUS represents a promising biomedical technology to remotely and safely ...

Engineering

Non-invasive Parenchymal, Vascular and Metabolic High-frequency Ultrasound and Photoacoustic Rat Deep Brain Imaging

Photoacoustics and high frequency ultrasound stands out as powerful tools for neurobiological applications enabling high-resolution imaging on the central nervous system of small animals. However, transdermal and transcranial neuroimaging is frequently affected by low sensitivity, image aberrations and loss of space resolution, requiring scalp or even skull removal before imaging. To overcome this challenge, a new protocol is presented to gain significant insights in brain hemodynamics by photoacoustic and high-frequency ultrasounds imaging with the animal skin and skull intact. The procedure relies on the passage of ultrasound (US) waves and laser directly through the fissures that are naturally present on the animal cranium. By juxtaposing the imaging transducer device exactly in correspondence to these selected areas where the skull has a reduced thickness or is totally absent, one can acquire high quality deep images and explore internal brain regions that are usually difficult to anatomically or functionally describe without an invasive approach. By applying this experimental procedure, significant data can be collected in both sonic and optoacoustic modalities, enabling to image the parenchymal and the vascular anatomy far below the head surface. Deep brain features such as parenchymal convolutions and fissures separating the lobes were clearly visible. Moreover, the configuration of large and small blood vessels was imaged at several millimeters of depth, and precise information were collected about blood fluxes, vascular stream velocities and the hemoglobin chemical state. This repertoire of data could be crucial in several research contests, ranging from brain vascular disease studies to experimental techniques involving the systemic administration of exogenous chemicals or other objects endowed with imaging contrast enhancement properties. In conclusion, thanks to the presented protocol, the US and PA techniques become an attractive noninvasive performance-competitive means for cortical and internal brain imaging, retaining a significant potential in many neurologic fields.

The present work describes a new protocol to perform non-invasive high-frequency ultrasound and photoacoustic based imaging on rat brain, to efficiently visualize deep subcortical regions and their vascular patterns by directing signals on skull foramina naturally present on animal cranium.

Photoacoustics and high frequency ultrasound stands out as powerful tools for neurobiological applications enabling high-resolution imaging on the central ...

Neuroscience

Multi-timescale Microscopy Methods for the Characterization of Fluorescently-labeled Microbubbles for Ultrasound-Triggered Drug Release

Microbubble contrast agents hold great promise for drug delivery applications with ultrasound. Encapsulating drugs in nanoparticles reduces systemic toxicity and increases circulation time of the drugs. In a novel approach to microbubble-assisted drug delivery, nanoparticles are incorporated in or on microbubble shells, enabling local and triggered release of the nanoparticle payload with ultrasound. A thorough understanding of the release mechanisms within the vast ultrasound parameter space is crucial for efficient and controlled release. This set of presented protocols is applicable to microbubbles with a shell containing a fluorescent label. Here, the focus is on microbubbles loaded with poly(2-ethyl-butyl cyanoacrylate) polymeric nanoparticles, doped with a modified Nile Red dye. The particles are fixed within a denatured casein shell. The microbubbles are produced by vigorous stirring, forming a dispersion of perfluoropropane gas in the liquid phase containing casein and nanoparticles, after which the microbubble shell self-assembles. A variety of microscopy techniques are needed to characterize the nanoparticle-stabilized microbubbles at all relevant timescales of the nanoparticle release process. Fluorescence of the nanoparticles enables confocal imaging of single microbubbles, revealing the particle distribution within the shell. In vitro ultra-high-speed imaging using bright-field microscopy at 10 million frames per second provides insight into the bubble dynamics in response to ultrasound insonation. Finally, nanoparticle release from the bubble shell is best visualized by means of fluorescence microscopy, performed at 500,000 frames per second. To characterize drug delivery in vivo, the triggered release of nanoparticles within the vasculature and their extravasation beyond the endothelial layer is studied using intravital microscopy in tumors implanted in dorsal skinfold window chambers, over a timescale of several minutes. The combination of these complementary characterization techniques provides unique insight into the behavior of microbubbles and their payload release at a range of time and length scales, both in vitro and in vivo.

The presented protocols can be used to characterize the response of fluorescently-labeled microbubbles designed for ultrasound-triggered drug delivery applications, including their activation mechanisms as well as their bioeffects. This paper covers a range of in vitro and in vivo microscopy techniques performed to capture the relevant length and timescales.

Microbubble contrast agents hold great promise for drug delivery applications with ultrasound. Encapsulating drugs in nanoparticles reduces systemic ...

A Benchtop Approach to the Location Specific Blood Brain Barrier Opening using Focused Ultrasound in a Rat Model

Stereotaxic surgery is the gold standard for localized drug and gene delivery to the rodent brain. This technique has many advantages over systemic delivery including precise localization to a target brain region and reduction of off target side effects. However, stereotaxic surgery is highly invasive which limits its translational efficacy, requires long recovery times, and provides challenges when targeting multiple brain regions. Focused ultrasound (FUS) can be used in combination with circulating microbubbles to transiently open the blood brain barrier (BBB) in millimeter sized regions. This allows intracranial localization of systemically delivered agents that cannot normally cross the BBB. This technique provides a noninvasive alternative to stereotaxic surgery. However, to date this technique has yet to be widely adopted in neuroscience laboratories due to the limited access to equipment and standardized methods. The overall goal of this protocol is to provide a benchtop approach to FUS BBB opening (BBBO) that is affordable and reproducible and can therefore be easily adopted by any laboratory.

Focused ultrasound with microbubble agents can open the blood brain barrier focally and transiently. This technique has been used to deliver a wide range of agents across the blood brain barrier. This article provides a detailed protocol for the localized delivery to the rodent brain with or without MRI guidance.

Stereotaxic surgery is the gold standard for localized drug and gene delivery to the rodent brain. This technique has many advantages over systemic ...

A High-Throughput Image-Guided Stereotactic Neuronavigation and Focused Ultrasound System for Blood-Brain Barrier Opening in Rodents

The blood-brain barrier (BBB) has been a major hurdle for the treatment of various brain diseases. Endothelial cells, connected by tight junctions, form a physiological barrier preventing large molecules (&#62;500 Da) from entering the brain tissue. Microbubble-mediated focused ultrasound (FUS) can be used to induce a transient local BBB opening, allowing larger drugs to enter the brain parenchyma.
In addition to large-scale clinical devices for clinical translation, preclinical research for therapy response assessment of drug candidates requires dedicated small animal ultrasound setups for targeted BBB opening. Preferably, these systems allow high-throughput workflows with both high-spatial precision as well as integrated cavitation monitoring, while still being cost effective in both initial investment and running costs.
Here, we present a bioluminescence and X-ray guided stereotactic small animal FUS system that is based on commercially available components and fulfills the aforementioned requirements. A particular emphasis has been placed on a high degree of automation facilitating the challenges typically encountered in high-volume preclinical drug evaluation studies. Examples of these challenges are the need for standardization in order to ensure data reproducibility, reduce intra-group variability, reduce sample size and thus comply with ethical requirements and decrease unnecessary workload. The proposed BBB system has been validated in the scope of BBB opening facilitated drug delivery trials on patient-derived xenograft models of glioblastoma multiforme and diffuse midline glioma.

The blood-brain barrier (BBB) can be temporarily disrupted with microbubble-mediated focused ultrasound (FUS). Here, we describe a step-by-step protocol for high-throughput BBB opening in vivo using a modular FUS system accessible for non-ultrasound experts.

The blood-brain barrier (BBB) has been a major hurdle for the treatment of various brain diseases. Endothelial cells, connected by tight junctions, form a ...

Focused Ultrasound Induced Blood-Brain Barrier Opening for Targeting Brain Structures and Evaluating Chemogenetic Neuromodulation

Acoustically Targeted Chemogenetics (ATAC) allows for the noninvasive control of specific neural circuits. ATAC achieves such control through a combination of focused ultrasound (FUS) induced blood-brain barrier opening (FUS-BBBO), gene delivery with adeno-associated viral (AAV) vectors, and activation of cellular signaling with engineered, chemogenetic, protein receptors and their cognate ligands. With ATAC, it is possible to transduce both large and small brain regions with millimeter precision using a single noninvasive ultrasound application. This transduction can later allow for a long-term, noninvasive, device-free neuromodulation in freely moving animals using a drug. Since FUS-BBBO, AAVs, and chemogenetics have been used in multiple animals, ATAC should also be scalable for the use in other animal species. This paper expands upon a previously published protocol and outlines how to optimize the gene delivery with FUS-BBBO to small brain regions with MRI-guidance but without a need for a complicated MRI-compatible FUS device. The protocol, also, describes the design of mouse targeting and restraint components that can be 3D-printed by any lab and can be easily modified for different species or custom equipment. To aid reproducibility, the protocol describes in detail how the microbubbles, AAVs, and venipuncture were used in ATAC development. Finally, an example data is shown to guide the preliminary investigations of studies utilizing ATAC.

This protocol delineates steps necessary for the gene delivery through focused ultrasound blood brain barrier (BBB) opening, evaluation of the resulting gene expression, and measurement of neuromodulation activity of chemogenetic receptors through histological tests.

Acoustically Targeted Chemogenetics (ATAC) allows for the noninvasive control of specific neural circuits. ATAC achieves such control through a ...

Two-Dimensional Super-Resolution Visualization of Rat Brain Microvasculature Using Ultrasound Localization Microscopy

The cerebral microvasculature forms a complex network of vessels essential for maintaining brain function. Diseases such as stroke, Alzheimer's disease, gliomas, and vascular dementia can profoundly disrupt the microvascular system. Unfortunately, current medical imaging modalities offer only indirect observations at this scale. Inspired by optical microscopy, ultrasound localization microscopy (ULM) overcomes the classical trade-off between penetration depth and spatial resolution. By localizing and tracking individual injected microbubbles (MBs) with sub-wavelength precision, vascular and velocity maps can be generated at the micrometer scale. Here, we present a robust protocol for super-resolution imaging of the brain microvasculature in vivo in rats using a commercial ultrasound platform. This method achieves 12.5 &#181;m spatial resolution, reconstructing the microvascular architecture and providing detailed information on blood flow direction and velocity, greatly enhancing our understanding of cerebral microcirculation. The protocol can be extended to rat disease models, offering a powerful tool for the early diagnosis and treatment of neurovascular diseases.

Here, we describe a protocol for ultrasound localization microscopy (ULM), which achieves 12.5 &#181;m spatial resolution to image the brain microvasculature in rats. It enables detailed visualization of blood flow direction and velocity, offering a powerful tool for advancing studies of cerebral circulation and vascular disorders.

The cerebral microvasculature forms a complex network of vessels essential for maintaining brain function. Diseases such as stroke, Alzheimer's disease, ...

Enhancing Drug Delivery to the Brain: MRI-Guided Ultrasound Techniques in Rats

Monitoring Blood-Brain Barrier Opening in Rats with a Preclinical Focused Ultrasound System

The brain has a highly selective semipermeable blood barrier, termed the blood-brain barrier (BBB), which prevents the delivery of therapeutic macromolecular agents to the brain. The integration of MR-guided low-intensity pulsed focused ultrasound (FUS) with microbubble pre-injection is a promising technique for non-invasive and non-toxic BBB modulation. MRI can offer superior soft-tissue contrast and various quantitative assessments, such as vascular permeability, perfusion, and the spatial-temporal distribution of MRI contrast agents. Notably, contrast-enhanced MRI techniques with gadolinium-based MR contrast agents have been shown to be the gold standard for detecting BBB openings. This study outlines a comprehensive methodology involving MRI protocols and animal procedures for monitoring BBB opening in a rat model. The rat model provides the added benefit of jugular vein catheter utilization, which facilitates rapid medication administration. A stereotactic-guided preclinical FUS transducer facilitates the refinement and streamlining of animal procedures and MRI protocols. The resulting methods are characterized by reproducibility and simplicity, eliminating the need for specialized surgical expertise. This research endeavors to contribute to the optimization of preclinical procedures with rat models and encourage further investigation into the modulation of the BBB to enhance therapeutic interventions in neurological disorders.

This study describes a combined magnetic resonance imaging (MRI) and low-intensity pulsed focused ultrasound (FUS) protocol, utilizing living rats with jugular vein catheterization to monitor blood-brain barrier (BBB) opening.

Real-Time Intravital Multiphoton Microscopy to Visualize Focused Ultrasound and Microbubble Treatments to Increase Blood-Brain Barrier Permeability

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