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 border="1" fo:keep-together.within-page="1" fo:keep-with-next.within-page="always">
	<tbody>
		<tr>
			<td>Ring transducer placement</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>Animal preparation and drugs</td>
			<td></td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>Bupivacaine*A</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*A</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*A</td>
			<td>Indivior</td>
			<td>521634</td>
			<td>Dose rat: 0.01-0.05 mg/kg, s.c..</td>
		</tr>
		<tr>
			<td>Carprofen*C</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*C</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*C</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*A</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*A</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&#233;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. A For acute window surgeries, C 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>Material and equipment for cranial window placement</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>Multiphoton microscopy</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>Ultrasound treatment</td>
			<td></td>
			<td></td>
			<td></td>
		</tr>
		<tr>
			<td>50 dB RF Amplifier</td>
			<td>E&#38;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

4.1K Views.  Sunnybrook Research Institute. 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.

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

Introduction to the Ultrasound Targeted Microbubble Destruction Technique

In UTMD, bioactive molecules, such as negatively charged plasmid DNA vectors encoding a gene of interest, are added to the cationic shells of lipid microbubble contrast agents7-9. In mice these vector-carrying microbubbles can be administered intravenously or directly to the left ventricle of the heart. In larger animals they can also be infused through an intracoronary catheter. The subsequent delivery from the circulation to a target organ occurs by acoustic cavitation at a resonant frequency of the microbubbles. It seems likely that the mechanical energy generated by the microbubble destruction results in transient pore formation in or between the endothelial cells of the microvasculature of the targeted region10. As a result of this sonoporation effect, the transfection efficiency into and across the endothelial cells is enhanced, and transgene-encoding vectors are deposited into the surrounding tissue. Plasmid DNA remaining in the circulation is rapidly degraded by nucleases in the blood, which further reduces the likelihood of delivery to non-sonicated tissues and leads to highly specific target-organ transfection.

Ultrasound Targeted Microbubble Destruction (UTMD) can be used to direct site-specific delivery of bioactive molecules, including therapeutic genes, to target organs accessible to ultrasound, such as the heart and liver1-6.

In UTMD, bioactive molecules, such as negatively charged plasmid DNA vectors encoding a gene of interest, are added to the cationic shells of lipid ...

Design of a Cyclic Pressure Bioreactor for the Ex Vivo Study of Aortic Heart Valves

The aortic valve, located between the left ventricle and the aorta, allows for unidirectional blood flow, preventing backflow into the ventricle. Aortic valve leaflets are composed of interstitial cells suspended within an extracellular matrix (ECM) and are lined with an endothelial cell monolayer. The valve withstands a harsh, dynamic environment and is constantly exposed to shear, flexion, tension, and compression. Research has shown calcific lesions in diseased valves occur in areas of high mechanical stress as a result of endothelial disruption or interstitial matrix damage1-3. Hence, it is not surprising that epidemiological studies have shown high blood pressure to be a leading risk factor in the onset of aortic valve disease4. 
The only treatment option currently available for valve disease is surgical replacement of the diseased valve with a bioprosthetic or mechanical valve5. Improved understanding of valve biology in response to physical stresses would help elucidate the mechanisms of valve pathogenesis. In turn, this could help in the development of non-invasive therapies such as pharmaceutical intervention or prevention. Several bioreactors have been previously developed to study the mechanobiology of native or engineered heart valves6-9. Pulsatile bioreactors have also been developed to study a range of tissues including cartilage10, bone11 and bladder12. The aim of this work was to develop a cyclic pressure system that could be used to elucidate the biological response of aortic valve leaflets to increased pressure loads. 
The system consisted of an acrylic chamber in which to place samples and produce cyclic pressure, viton diaphragm solenoid valves to control the timing of the pressure cycle, and a computer to control electrical devices. The pressure was monitored using a pressure transducer, and the signal was conditioned using a load cell conditioner. A LabVIEW program regulated the pressure using an analog device to pump compressed air into the system at the appropriate rate. The system mimicked the dynamic transvalvular pressure levels associated with the aortic valve; a saw tooth wave produced a gradual increase in pressure, typical of the transvalvular pressure gradient that is present across the valve during diastole, followed by a sharp pressure drop depicting valve opening in systole. The LabVIEW program allowed users to control the magnitude and frequency of cyclic pressure. The system was able to subject tissue samples to physiological and pathological pressure conditions. This device can be used to increase our understanding of how heart valves respond to changes in the local mechanical environment.

Design of a Cyclic Pressure Bioreactor for the Ex Vivo Study of Aortic Heart Valves

A cyclic pressure bioreactor capable of subjecting heart valve tissue to physiological and pathological pressure conditions has been designed. A LabVIEW program allows users to control pressure magnitude, amplitude and frequency. This device can be used to study the mechanobiology of heart valve tissue or isolated cells.

The aortic valve, located between the left ventricle and the aorta, allows for unidirectional blood flow, preventing backflow into the ventricle. Aortic ...

Improved Method for the Preparation of a Human Cell-based, Contact Model of the Blood-Brain Barrier

The blood-brain barrier (BBB) comprises impermeable but adaptable brain capillaries which tightly control the brain environment. Failure of the BBB has been implied in the etiology of many brain pathologies, creating a need for development of human in vitro BBB models to assist in clinically-relevant research. Among the numerous BBB models thus far described, a static (without flow), contact BBB model, where astrocytes and brain endothelial cells (BECs) are cocultured on the opposite sides of a porous membrane, emerged as a simplified yet authentic system to simulate the BBB with high throughput screening capacity. Nevertheless the generation of such model presents few technical challenges. Here, we describe a protocol for preparation of a contact human BBB model utilizing a novel combination of primary human BECs and immortalized human astrocytes. Specifically, we detail an innovative method for cell-seeding on inverted inserts as well as specify insert staining techniques and exemplify how we use our model for BBB-related research.

Establishment of human models of the blood-brain barrier (BBB) can benefit research into brain conditions associated with BBB failure. We describe here an improved technique for preparation of a contact BBB model, which permits coculturing of human astrocytes and brain endothelial cells on the opposite sides of a porous membrane.

The blood-brain barrier (BBB) comprises impermeable but adaptable brain capillaries which tightly control the brain environment. Failure of the BBB has ...

Real-time Monitoring of High Intensity Focused Ultrasound (HIFU) Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound (HMIFU)

Harmonic Motion Imaging for Focused Ultrasound (HMIFU) is a technique that can perform and monitor high-intensity focused ultrasound (HIFU) ablation. An oscillatory motion is generated at the focus of a 93-element and 4.5 MHz center frequency HIFU transducer by applying a 25 Hz amplitude-modulated signal using a function generator. A 64-element and 2.5 MHz imaging transducer with 68kPa peak pressure is confocally placed at the center of the HIFU transducer to acquire the radio-frequency (RF) channel data. In this protocol, real-time monitoring of thermal ablation using HIFU with an acoustic power of 7 W on canine livers in vitro is described. HIFU treatment is applied on the tissue during 2 min and the ablated region is imaged in real-time using diverging or plane wave imaging up to 1,000 frames/second. The matrix of RF channel data is multiplied by a sparse matrix for image reconstruction. The reconstructed field of view is of 90&#176; for diverging wave and 20 mm for plane wave imaging and the data are sampled at 80 MHz. The reconstruction is performed on a Graphical Processing Unit (GPU) in order to image in real-time at a 4.5 display frame rate. 1-D normalized cross-correlation of the reconstructed RF data is used to estimate axial displacements in the focal region. The magnitude of the peak-to-peak displacement at the focal depth decreases during the thermal ablation which denotes stiffening of the tissue due to the formation of a lesion. The displacement signal-to-noise ratio (SNRd) at the focal area for plane wave was 1.4 times higher than for diverging wave showing that plane wave imaging appears to produce better displacement maps quality for HMIFU than diverging wave imaging.

Real-time Monitoring of High Intensity Focused Ultrasound HIFU Ablation of In Vitro Canine Livers Using Harmonic Motion Imaging for Focused Ultrasound HMIFU

This article describes real-time monitoring of HIFU ablation in canine liver with high frame rate ultrasound imaging using diverging and plane wave imaging. Harmonic Motion Imaging for Focused Ultrasound is used to image the decrease of acoustic radiation force induced displacement in the ablated region.

Harmonic Motion Imaging for Focused Ultrasound (HMIFU) is a technique that can perform and monitor high-intensity focused ultrasound (HIFU) ablation. An ...

In Vitro Permeation of FITC-loaded Ferritins Across a Rat Blood-brain Barrier: a Model to Study the Delivery of Nanoformulated Molecules

Brain microvascular endothelial cells, supported by pericytes and astrocytes endfeet, are responsible for the low permeation of large hydrosoluble drugs through the blood-brain barrier (BBB), causing difficulties for effective pharmacological therapies. In recent years, different strategies for promoting brain targeting have aimed to improve drug delivery and activity at this site, including innovative nanosystems for drug delivery across the BBB. In this context, an in vitro approach based on a simplified cellular model of the BBB provides a useful tool to investigate the effect of nanoformulations on the trans-BBB permeation of molecules. This study describes the development of a double-layer BBB, consisting of co-cultured commercially available primary rat brain microvascular endothelial cells and astrocytes. A multiparametric approach for the validation of the model, based on the measurement of the transendothelial electrical resistance and the apparent permeability of a high molecular weight dextran, is also described. As proof of concept for the employment of this BBB model to study the effect of different nanoformulations on the translocation of fluorescent molecules across the barrier, we describe the use of fluorescein isothiocyanate (FITC), loaded into ferritin nanoparticles. The ability of ferritins to improve the trans-BBB permeation of FITC was demonstrated by flux measurements and confocal microscopy analyses. The results suggest this is a useful system for validating nanosystems for delivery of drugs across the BBB.

In Vitro Permeation of FITC-loaded Ferritins Across a Rat Blood-brain Barrier: a Model to Study the Delivery of Nanoformulated Molecules

A method to establish an in vitro model of blood-brain barrier based on a co-culture of rat brain microvascular endothelial cells and astrocytes is described and validated. This system proved to be a valid tool to study the effect of nanoformulation on the trans-barrier permeation of fluorescent molecules.

Brain microvascular endothelial cells, supported by pericytes and astrocytes endfeet, are responsible for the low permeation of large hydrosoluble drugs ...

In Situ Microscopy for Real-time Determination of Single-cell Morphology in Bioprocesses

In situ monitoring in microbial bioprocesses is mostly restricted to chemical and physical properties of the medium (e.g.,pH value and the dissolved oxygen concentration). Nevertheless, the morphology of cells can be a suitable indicator for optimal conditions, since it changes with dependence on the growth state, product accumulation and cell stress. Furthermore, the single-cell size distribution provides not only information about the cultivation conditions, but also about the population heterogeneity. To gain such information, a photo-optical in situ microscopy device1 was developed to enable the monitoring of the single-cell size distribution directly in the cell suspension in bioreactors. An automated image analysis is coupled to the microscopy based on a neural network model, which is trained with user-annotated images. Several parameters, which are gained from the captures of the microscope, are correlated to process relevant features of the cells, like their metabolic activity. Until now, the presented in situ microscopy probe series was applied to measure the pellet size in filamentous fungi suspensions. It was used to distinguish the single-cell size in microalgae cultivation and relate it to lipid accumulation. The shape of cellular particles was related to budding in yeast cultures. The microscopy analysis can be generally split into three steps: (i) image acquisition, (ii) particle identification, and (iii) data analysis, respectively. All steps have to be adapted to the organism, and therefore specific annotated information is required in order to achieve reliable results. The ability to monitor changes in cell morphology directly in line or on line (in a by-pass) enables real-time values for monitoring and control, in process development as well as in production scale. If the off line data correlates with the real-time data, the current tedious off line measurements with unknown influences on the cell size become needless.

In Situ Microscopy for Real-time Determination of Single-cell Morphology in Bioprocesses

A photo-optical in situ microscopy device was developed to monitor the size of single cells directly in the cell suspension. The real-time measurement is conducted by coupling the photo-optical sterilizable probe to an automated image analysis. Morphological changes appear with dependence on the growth state and cultivation conditions.

In situ monitoring in microbial bioprocesses is mostly restricted to chemical and physical properties of the medium (e.g.,pH value and the dissolved ...

Real-time Visualization and Analysis of Chondrocyte Injury Due to Mechanical Loading in Fully Intact Murine Cartilage Explants

Homeostasis of articular cartilage depends on the viability of resident cells (chondrocytes). Unfortunately, mechanical trauma can induce widespread chondrocyte death, potentially leading to irreversible breakdown of the joint and the onset of osteoarthritis. Additionally, maintenance of chondrocyte viability is important in osteochondral graft procedures for optimal surgical outcomes. We present a method to assess the spatial extent of cell injury/death on the articular surface of intact murine synovial joints after application of controlled mechanical loads or impacts. This method can be used in comparative studies to investigate the effects of different mechanical loading regimens, different environmental conditions or genetic manipulations, as well as different stages of cartilage degeneration on short- and/or long-term vulnerability of in situ articular chondrocytes. The goal of the protocol introduced in the manuscript is to assess the spatial extent of cell injury/death on the articular surface of murine synovial joints. Importantly, this method enables testing on fully intact cartilage without compromising native boundary conditions. Moreover, it allows for real-time visualization of vitally stained articular chondrocytes and single image-based analysis of cell injury induced by application of controlled static and impact loading regimens. Our representative results demonstrate that in healthy cartilage explants, the spatial extent of cell injury depends sensitively on load magnitude and impact intensity. Our method can be easily adapted to investigate the effects of different mechanical loading regimens, different environmental conditions or different genetic manipulations on the mechanical vulnerability of in situ articular chondrocytes.

We present a method to assess the spatial extent of cell injury/death on the articular surface of intact murine joints after application of controlled mechanical loads or impacts. This method can be used to investigate how osteoarthritis, genetic factors and/or different loading regimens affect the vulnerability of in situ chondrocytes.

Homeostasis of articular cartilage depends on the viability of resident cells (chondrocytes). Unfortunately, mechanical trauma can induce widespread ...

Lucifer Yellow - A Robust Paracellular Permeability Marker in a Cell Model of the Human Blood-brain Barrier

The blood-brain barrier BBB consists of endothelial cells that form a barrier between the systemic circulation and the brain to prevent the exchange of non-essential ions and toxic substances. Tight junctions (TJ) effectively seal the paracellular space in the monolayers resulting in an intact barrier. This study describes a LY-based fluorescence assay that can be used to determine its apparent permeability coefficient (Papp) and in turn can be used to determine the kinetics of the formation of confluent monolayers and the resulting tight junction barrier integrity in hCMEC/D3 monolayers. We further demonstrate an additional utility of this assay to determine TJ functional integrity in transfected cells. Our data from the LY Papp assay shows that the hCMEC/D3 cells seeded in a transwell setup effectively limit LY paracellular transport 7 days-post culture. As an additional utility of the presented assay, we also demonstrate that the DNA nanoparticle transfection does not alter LY paracellular transport in hCMEC/D3 monolayers.

We present a fluorescence assay to demonstrate that Lucifer Yellow (LY) is a robust marker to determine the apparent paracellular permeability of hCMEC/D3 cell monolayers, an in vitro model of the human blood-brain barrier. We used this assay to determine the kinetics of a confluent monolayer formation in cultured hCMEC/D3 cells.

The blood-brain barrier BBB consists of endothelial cells that form a barrier between the systemic circulation and the brain to prevent the exchange of ...

A Custom Multiphoton Microscopy Platform for Live Imaging of Mouse Cornea and Conjunctiva

Conventional histological analysis and cell culture systems are insufficient to simulate in vivo physiological and pathological dynamics completely. Multiphoton microscopy (MPM) has become one of the most popular imaging modalities for biomedical study at cellular levels in vivo, advantages include high resolution, deep tissue penetration and minimal phototoxicity. We have designed an MPM imaging platform with a customized mouse eye holder and a stereotaxic stage for imaging ocular surface in vivo. Dual fluorescent protein reporter mouse enables visualization of cell nuclei, cell membranes, nerve fibers, and capillaries within the ocular surface. In addition to multiphoton fluorescence signals, acquiring second harmonic generation (SHG) simultaneously allows for the characterization of collagenous stromal architecture. This platform can be employed for intravital imaging with accurate positioning across the entire ocular surface, including cornea and conjunctiva.

Presented here is a multiphoton microscopic platform for live mouse ocular surface imaging. Fluorescent transgenic mouse enables the visualization of cell nuclei, cell membranes, nerve fibers and capillaries within the ocular surface. Non-linear second harmonic generation signals derived from collagenous structures provide label-free imaging for stromal architectures.

Conventional histological analysis and cell culture systems are insufficient to simulate in vivo physiological and pathological dynamics completely. ...

Residue-Specific Exchange of Proline by Proline Analogs in Fluorescent Proteins: How "Molecular Surgery" of the Backbone Affects Folding and Stability

Replacement of proline (Pro) residues in proteins by the traditional site-directed mutagenesis by any of the remaining 19 canonical amino acids is often detrimental to protein folding and, in particular, chromophore maturation in green fluorescent proteins and related variants. A reasonable alternative is to manipulate the translation of the protein so that all Pro residues are replaced residue-specifically by analogs, a method known as selective pressure incorporation (SPI). The built-in chemical modifications can be used as a kind of &#34;molecular surgery&#34; to finely dissect measurable changes or even rationally manipulate different protein properties. Here, the study demonstrates the usefulness of the SPI method to study the role of prolines in the organization of the typical &#946;-barrel structure of spectral variants of the green fluorescent protein (GFP) with 10-15 prolines in their sequence: enhanced green fluorescent protein (EGFP), NowGFP, and KillerOrange. Pro residues are present in connecting sections between individual &#946;-strands and constitute the closing lids of the barrel scaffold, thus being responsible for insulation of the chromophore from water, i.e., fluorescence properties. Selective pressure incorporation experiments with (4R)-fluoroproline (R-Flp), (4S)-fluoroproline (S-Flp), 4,4-difluoroproline (Dfp), and 3,4-dehydroproline (Dhp) were performed using a proline-auxotrophic E. coli strain as expression host. We found that fluorescent proteins with S-Flp and Dhp are active (i.e., fluorescent), while the other two analogs (Dfp and R-Flp) produced dysfunctional, misfolded proteins. Inspection of UV-Vis absorption and fluorescence emission profiles showed few characteristic alterations in the proteins containing Pro analogs. Examination of the folding kinetic profiles in EGFP variants showed an accelerated refolding process in the presence of S-Flp, while the process was similar to wild-type in the protein containing Dhp. This study showcases the capacity of the SPI method to produce subtle modifications of protein residues at an atomic level (&#34;molecular surgery&#34;), which can be adopted for the study of other proteins of interest. It illustrates the outcomes of proline replacements with close chemical analogs on the folding and spectroscopic properties in the class of &#946;-barrel fluorescent proteins.

To overcome the limitations of classical site-directed mutagenesis, proline analogs with specific modifications were incorporated into several fluorescent proteins. We show how the replacement of hydrogen by fluorine or of the single by double bonds in proline residues ("molecular surgery") affects fundamental protein properties, including their folding and interaction with light.

Replacement of proline (Pro) residues in proteins by the traditional site-directed mutagenesis by any of the remaining 19 canonical amino acids is often ...