Theranostics 2020; 10(17):7758-7774. doi:10.7150/thno.46821
A Porcine Model of Transvertebral Ultrasound and Microbubble-Mediated Blood-Spinal Cord Barrier Opening
1. Physical Sciences Platform, Sunnybrook Research Institute, Toronto, ON, Canada.
2. Department of Medical Biophysics, University of Toronto, Toronto, ON, Canada.
Fletcher SMP, Choi M, Ogrodnik N, O'Reilly MA. A Porcine Model of Transvertebral Ultrasound and Microbubble-Mediated Blood-Spinal Cord Barrier Opening. Theranostics 2020; 10(17):7758-7774. doi:10.7150/thno.46821. Available from http://www.thno.org/v10p7758.htm
Blood-spinal cord barrier opening, using focused ultrasound and microbubbles, has the potential to improve drug delivery for the treatment of spinal cord pathologies. Delivering and detecting ultrasound through the spine is a challenge for clinical translation. We have previously developed short burst, phase keying exposures, which can be used in a dual-aperture configuration to address clinical scale targeting challenges. Here we demonstrate the use of these pulses for blood-spinal cord barrier opening, in vivo in pigs.
Methods: The spinal cords of Yorkshire pigs (n=8) were targeted through the vertebral laminae, in the lower thoracic to upper lumbar region using focused ultrasound (486 kHz) and microbubbles. Four animals were treated with a combination of pulsed sinusoidal exposures (1.0-4.0 MPa, non-derated) and pulsed short burst, phase keying exposures (1.0-2.0 MPa, non-derated). Four animals were treated using ramped short burst, phase keying exposures (1.8-2.1 MPa, non-derated). A 250 kHz narrowband receiver was used to detect acoustic emissions from microbubbles. Blood-spinal cord barrier opening was assessed by the extravasation of Evans blue dye. Histological analysis of the spinal cords was used to assess tissue damage and excised vertebral samples were used in benchtop experiments.
Results: Ramped short burst, phase keying exposures successfully modified the blood-spinal cord barrier at 16/24 targeted locations, as assessed by the extravasation of Evans blue dye. At 4 of these locations, opening was confirmed with minimal adverse effects observed through histology. Transmission measurements through excised vertebrae indicated a mean transmission of (47.0 ± 7.0 %) to the target.
Conclusions: This study presents the first evidence of focused ultrasound-induced blood-spinal cord barrier opening in a large animal model, through the intact spine. This represents an important step towards clinical translation.
Keywords: Focused ultrasound, blood-spinal cord barrier opening, drug delivery, spinal cord therapy, microbubbles
Diseases and disorders of the central nervous system (CNS) pose a unique challenge to conventional methods of drug delivery due to the presence of the blood-brain and blood-spinal cord barriers (BBB and BSCB) [1,2]. These are neurovascular units, characterized by a physical barrier, consisting of non-fenestrated endothelial cells with tight junctions, and a transport barrier due to membrane transporter proteins and vesicular mechanisms . Together, these limit both transcellular and paracellular transport of foreign molecules, including therapeutics, from blood into the CNS parenchyma. Consequently, only a small class of drugs with low molecular weight (< 500 Da) and high lipophilicity are able to cross these barriers in therapeutically relevant quantities .
One promising method for bypassing these barriers is the use of focused ultrasound (FUS) in conjunction with intravenously injected ultrasound contrast agents or microbubbles (MBs) . When MBs in the vasculature are sonicated with FUS, they oscillate and interact with vessel walls leading to a range of bioeffects  which result in the localized and transient opening of the CNS barriers. Because MBs are strong nonlinear scatterers of ultrasound, acoustic emissions from oscillating MBs in the vasculature can be monitored to assess treatment efficacy and potential for tissue damage [6,7]. For pulsed FUS sonications, on the order of milliseconds, the presence of spectral frequency signatures have been well characterized: those associated with stable MB oscillation, like harmonic emissions, have been linked to successful barrier opening, while those associated with inertial cavitation and MB collapse, like broadband emissions, have been linked to widespread tissue damage. The understanding of the correlation between spectral signatures and tissue bioeffects has allowed the development of real-time acoustic emissions based control algorithms to promote safe and effective treatments [8-12].
In the brain, there have been a large number of preclinical studies demonstrating the increased permeability of the BBB to tracers and therapeutic agents following FUS + MB treatments [13-19]. Recently, FUS-induced BBB opening (BBBO) has reached the stage of clinical trials for treatment of primary brain tumours  and early to moderate stage Alzheimer's disease . There has been markedly less effort towards translating this method to the spinal cord. However, in the past decade, preliminary research in animal models has indicated that the BSCB can be modified using FUS + MBs, similarly to the BBB [22-27]. To date, these studies have been limited to transvertebral studies in rodents [22-26], in which the thickness and density of vertebral bone is not comparable with humans, or in rabbits, which have included pre-treatment laminectomies . Although a laminectomy may be appropriate in cases of injury or focal tumors, there is a need to develop non-invasive approaches through the intact bone for this treatment to be relevant to diffuse disease, such as leptomeningeal metastases  or neurodegenerative diseases, like multiple sclerosis  or amyotrophic lateral sclerosis , where treatment along large portions of the neuroaxis is required.
The challenges that must be overcome to safely and efficiently deliver FUS and detect acoustic emissions through the human spine are non-trivial. Developing robust solutions to combat these challenges is essential for clinical translation. Phased arrays tailored to the spinal geometry may provide an opportunity to overcome the low FUS transmission (~ 31 ± 17% at 514 kHz) and high levels of focal distortion that arise as sound propagates through vertebral bone [31,32]. At the submegahertz frequencies needed to minimize attenuation and aberration , the focal size is large compared to the size of the spinal canal. Due to reflections off the interior walls of the spinal canal, this situation is prone to the formation of standing waves which can compromise treatment safety . To address this, a dual aperture, cross-beam approach through the vertebral laminae using short burst, phase keying (SBPK) exposures has been proposed . SBPK FUS exposures can be modified to leverage pulse inversion (PI)  to enhance detection of MB emissions through the intact spine . SBPK FUS exposures have been shown to successfully open the BSCB in small animals, by our group .
An important step towards clinical translation is testing these proposed methods in a clinically relevant, large animal model, where spinal geometry is comparable with humans. The porcine spine has previously been identified as a good anatomical model of the human spine in the mid to low thoracic region .
In this work, we present a model of FUS-induced BSCB opening (BSCBO) through the intact porcine spine, using SBPK exposures.
Two in-house fabricated, spherically focused, piezocomposite lead zirconium titanate (PZT) transducers with a center frequency (f0) of 486kHz were used for these experiments (DL-47 composite elements sourced from DeL Piezo Specialties, LLC, FL, USA; aperture diameter = 5 cm; nominal focal length = 10 cm). Each transducer had a 5 mm bore into which acoustic receivers could be inserted. The transducers were driven using a dual-channel arbitrary function generator (AFG 31000 Series, Tektronix, Beaverton, OR, USA) and two 53 dB RF power amplifiers (NP-2519, NP Technologies Inc., Newbury Park, CA, USA). An in-house fabricated unfocussed, narrowband 5 mm PZT receiver (DL-47 element sourced from DeL Piezo Specialties) with a center frequency of 250 kHz (near the subharmonic (f0/2)) was used in this experiment.
In the confocal, dual-aperture configuration (Figure 1A), using SBPK pulse trains, the focal dimensions (70% pressure profile) were 8.4 × 4.5 × 4.7 mm3. The pressure at the focus of the transducers for a given driving voltage was calibrated by performing field scans in a tank of degassed and deionized water using a 0.5 mm polyvinylidene difluoride (PVDF) hydrophone of known calibration (Precision Acoustics, Dorchester, UK) mounted on a 3D positioning stage (Velmex Inc., Bloomfield, NY, USA). The 3D positioning stage was controlled using MATLAB. Hydrophone data were displayed using a mixed-domain oscilloscope (MDO 3014, Tektronix, Beaverton, OR, USA) and subsequently uploaded to a PC and stored for processing in MATLAB. A schematic diagram of the set up used for transducer calibration is shown in Figure 1B. Transducers were calibrated using both long (30 cycles), sinusoidal exposures and SBPK exposures.
Both 10 ms sinusoidal bursts and SBPK exposures were investigated for BSCBO in this study. Prior to experiments, two SBPK pulse trains, one for each transducer were generated in MATLAB and uploaded to the dual-channel arbitrary function generator. Figure 2A shows segments of the pulses generated in MATLAB, while Figures 2B and C show waveforms measured on the benchtop at the focus of both transducers using the PVDF needle hydrophone.
Focused Ultrasound Treatments
All animal experiments were approved by the Sunnybrook Research Institute animal care committee and were performed in keeping with guidelines from the Canadian Council on Animal Care. Eight (8) Yorkshire pigs (32.6 - 40.0 kg; Male; Lakeview Swine, Wallacetown, ON, Canada) were treated. To accommodate space constraints of the experimental set up, animals were requested from the supplier based on weight. Based on growth curves for Yorkshire pigs , the animals were estimated to be in the age range of 10-12 weeks at the time of treatment.
Animals were anaesthetized with ketamine (20 mg/kg, Narketan 10, Vetoquinol N.-A. Inc., Lavaltrie, QC, Canada) and atropine (0.02mg/kg, Teligent Canada, Mississauga, ON, Canada), intubated and maintained under anaesthesia using isoflurane (2%, Isoflurane USP, Fresenius Kabi Canada, Toronto, ON, Canada) and oxygen with medical ventilation. Prior to ultrasound exposures, the carrier gas was switched to medical air. To prevent an adverse reaction to the MBs [38-40], two (2) pigs were given intramuscular (IM) dexamethasone (0.5 mg/kg, Sandoz Canada, Boucherville, QC, Canada) twice a day for two days prior to the treatment. On treatment day, these pigs were administered an additional dose of dexamethasone (0.5 mg/kg). They were also administered a nonsteroidal, anti-inflammatory drug, meloxicam (0.4 mg/kg, Metacam, Boehringer Ingelheim Animal Health Canada Inc., Burlington, ON, Canada), for two days prior to the treatment and on treatment day. On treatment day, 30 min before the first treatment, intravascular (IV) diphenhydramine (0.5 mg/kg, Sandoz Canada, Boucherville, QC, Canada), an antihistamine, was administered. This drug cocktail was discontinued for the remaining six (6) animals and replaced with diphenhydramine (0.5 mg/kg) alone, administered in two half doses prior to the experiments. This change was made because the dexamethasone/meloxicam/diphenhydramine cocktail was found to restrict BSCBO. This is discussed further in the results and discussion sections. In animals receiving diphenhydramine alone, the first half dose was given IM after ketamine/atropine anaesthetization. The second half dose was diluted in 10 mL saline and given IV 30 min prior to the first treatment as a bolus injection. During experiments, heart rate and blood oxygenation levels were monitored in real time using a pulse oximeter (GE Datex-Ohmeda Pulse Oximeter- MRI Monitor, GE Healthcare, Chicago, IL, USA).
Schematic diagrams of (A) the confocal, dual-aperture configuration and (B) the set up used for transducer calibration in a scan tank.(Click on the image to enlarge.)
Short burst phase keying (SBPK) pulses generated in MATLAB (A) and, (B) and (C) measured at the focus using a polyvinylidene difluoride needle hydrophone. The waveform shown in (C) is a zoomed version of (B), indicated by the red box in (B). (C) shows the characteristics of SBPK exposures at the focus, including inverted pulse pairs and varying resultant magnitudes due to the interference of phase shifted pulses from the two transducers.(Click on the image to enlarge.)
Following treatments, Evans blue dye (EBD) (4% weight per volume saline dilution, 2 mL/kg, Thermo Fisher Scientific, Waltham, MA, USA) was administered IV, as a bolus, and allowed to circulate for 1.5 h to assess BSCBO. In pigs 1-6, EBD was administered following a period of post treatment magnetic resonance imaging (MRI) (~1hr), while in pigs 7&8, EBD was administered immediately following the last treatment, prior to post treatment MRI. In pigs 7&8, a greater number of sonications were performed and the decision to administer EBD prior to the last treatment was made in an effort to keep the time between the first sonication and EBD administration to a minimum.
Spinal cords were formalin fixed through transcardial perfusion with saline followed by 10% neutral buffered formalin under deep anesthetic and harvested for histological staining. Posterior elements of vertebrae in the treatment region were removed and stored in formalin for use in benchtop experiments to estimate ultrasound transmission through the spine. In one (1) animal, three (3) whole vertebrae above and below the treatment region were also removed. The final four (4) pigs were given heparin (500 IU/kg, Heparin LEO, LEO Pharma Inc., Thornhill, ON, Canada) 30 min prior to perfusion to minimize blood clotting during perfusion.
Animals were placed supine on top of a MRI compatible FUS system (LP-100, FUS Instruments, Toronto, ON, Canada) within the bore of a 3T MRI (3T Biograph mMR, Siemens Healthineers AG, Erlngen, Germany). The dual aperture transducer set up was mounted on a 3-axis positioning arm contained in the water bath of the FUS system. Treatment locations in the lower thoracic to upper lumbar region within the spinal cord were selected and targeted under MRI-guidance. The ribs were used as anatomical landmarks, with the highest treatment location between T11-T13. Diagrams showing the set up for treatments are shown in Figure 3 and a schematic of the treatment workflow is shown in Figure 4. A supine position of the animals minimized the effects of motion due to breathing. To stabilize the animals in this position, towel rolls were placed on either side of the pigs and the animals were tightly secured to the bed of the MRI. Pre- and post-treatment images were compared to confirm that movement of the animals had not occurred during the experiments. Targets within the spinal cord were selected using coronal T1 weighted MRI (GRE, Field of view = 20 × 20 cm2, spatial discretization = 0.4 mm, Slice thickness = 1.5 mm, Echo time = 2.46 s, Repetition time = 7 s, Rare factor = 1, Number of averages = 12). A flex coil placed across the chest of the animal above the FUS targeted region was used to improve the image signal-to-noise ratio (SNR). The experimental setup (animal supine on the FUS treatment platform) prevented placing the coil closer to the imaging region.
The treatment parameters for the eight (8) animals are shown in Table 1. Pigs 1-4 were pilot animals, used to demonstrate feasibility of BSCBO. These animals were treated using both sinusoidal bursts (10 ms, 1 Hz PRF, 2 min duration) and SBPK pulse trains (10 ms, 1 Hz PRF, 5 min duration). The non-derated pressures used for these animals were between 1 MPa and 4 MPa for sinusoidal bursts and between 1 MPa and 2 MPa for SBPK exposures. Once the potential for BSCBO had been established, four (4) animals (pigs 5-8) were treated at 2-10 locations per spinal cord, 10 mm apart, using ramped pressure SBPK exposures (10 ms pulse trains, 1 Hz PRF, 5 min). For these, pressures were ramped from 1.8 MPa to 2.1 MPa (non-derated) in 3 kPa increments over 2 min. A minimum of 8 treatment locations were intended in pigs 5-8. The varying number of sonications was a result of technical challenges encountered on the experiment days that limited the number of sonications performed in pigs 5 and 6.
For each treatment, MBs (0.005-0.010mL/kg, Definity, Lantheus Medical Imaging, MA, USA) were infused IV over 2 min. (The MB dose for pigs 1-5 was 0.010mL/kg. In pig 5, an increase in heart rate was observed following MB infusion. While vitals did return to normal, out of an abundance of caution, the MB dose was reduced to 0.005mL/kg for pigs 6-8.) FUS sonication commenced 30 s after the start of the infusion. A 250 kHz narrowband receiver was used to acquire acoustic emissions from MBs during treatments. Acquired waveforms were digitized using a two-channel 14-bit PCI scope card (ATS460, Alazar Technologies Inc., QC, Canada). For pigs 5-8, the frequency content of acoustic emissions, analyzed as described in , were plotted in real time and a detectable change in the subharmonic was used to trigger a 50% pressure drop, as described in . If a pressure change was triggered, the pressure was maintained at 50% of the trigger level for the duration of the treatment. If a pressure change was not triggered, the pressure was maintained at the maximum pressure (2.1 MPa) for the final 3 min of the treatment.
Treatment parameters used during experiments
|Pig ID||Pulse Type||Number of Treatments||Location Spacing (mm)||Pressure||Notes|
|1||SBPK||3||1. Fixed (1.5 MPa)||Dexamethasone and meloxicam|
|2. Fixed (2.0 MPa)||4 point square grids (3mmx3mm)|
|3. Fixed (1.0 MPa)||3mm spacing|
|2||Sine||2||1. Fixed (2.0 MPa)||Dexamethasone and meloxicam|
|2. Fixed (4.0 MPa)||3-5 points per treatment, 4mm spacing|
|SBPK||1||1. Fixed (2.0 MPa)|
|3||Sine||4||1. Fixed (1.5 MPa)||4 point square grids (3mmx3mm)|
|2. Fixed (2.0 MPa)||3mm spacing|
|3. Fixed (2.0 MPa)||All points overlapping|
|4. Fixed (3.0 MPa)|
|4||Sine||2||1. Fixed (1.0 MPa)||3 points per treatment, 5mm spacing|
|2. Fixed (4.0 MPa)|
|SBPK||1||1. Fixed (2.0 MPa)|
|5||SBPK||2||10||Ramp (1.8-2.1 MPa)||Single point sonications|
|6||SBPK||4||10||Ramp (1.8-2.1 MPa)||Single point sonications|
|7||SBPK||8||10||Ramp (1.8-2.1 MPa)||Single point sonications|
|8||SBPK||10||10||Ramp (1.8-2.1 MPa)||Single point sonications|
Schematic diagrams of (A) a sagittal view and (B) an axial view of the experimental set ups for treatments. (C) shows an axial magnetic resonance localizer image showing the experimental set up.(Click on the image to enlarge.)
A schematic diagram showing a flowchart of the experimental procedure for each pig.(Click on the image to enlarge.)
Description of histology grades
|0||No damage on all histology levels|
|1||Very minor damage - 1 to a few very small clusters of red blood cells on at least 1 histology level|
|2||Moderate (more significant) damage - 1 larger cluster of red blood cells or a greater number of small clusters of red blood cells on at least 1 histology level|
|3||Extensive damage - A large number of clusters of red blood cell extravasation, with or without pooling on at least 1 histology level.|
Following treatments, contrast enhanced (0.1mL/kg Gadovist (IV), Bayer Inc., NJ, USA) T1-weighted MR images were acquired using the parameters used for targeting, to assess BSCBO. For pig 8, additional coronal and sagittal contrast-enhanced, T1-weighted images (FLAIR, Field of view = 20 × 20 cm2, spatial discretization = 0.6 mm, Slice thickness = 1 mm, Echo time = 22 ms, Repetition time = 2 s, Inversion time = 860 ms, Rare factor = 5, Number of averages = 12) were acquired once all treatments were completed, removing the animal from the FUS treatment platform and imaging on the spine coils built into the MRI table. MR images were analyzed using Medical Image Processing, Analysis and Visualization (MIPAV; National Institutes of Health, Bethesda, MD, USA). BSCBO was confirmed if the mean MRI signal in a 3×3 voxel area centered on maximum enhancement was at least 2 standard deviations greater than the mean signal in a baseline 3×3 voxel unsonicated area in the spinal cord.
5 µm thick coronal sections at 100 µm intervals were stained using hematoxylin and eosin (H&E) and evaluated for tissue damage. Tissue damage at each treatment location was graded using a 4 point grading scheme adapted from . A description of each grade is shown in Table 2.
The posterior spinal segments that were removed after perfusions were used in benchtop experiments to estimate ultrasound transmission through the spine and update pressure estimates from the transducer calibration. The experimental setup used was similar to that used for transducer calibration (Figure 1B). Samples were degassed for several days in a vacuum jar, until no air bubbles were observed. On the day of the experiments, samples were degassed for 3 h in a vacuum jar prior to measurements. Posterior spinal (vertebral arch) samples from four (4) pigs (28.8-40.0kg) were placed between the transducers and the hydrophone. Field scans were performed with the interior surface of the vertebral arch positioned 6 mm pre-focal to the focal location as measured in water. Field scans were performed along three perpendicular planes with dimensions of 6 × 6 mm2. Vertebrae were translated along the sagittal plane (increments of 2.5 mm) to account for differences in transmission owing to vast inhomogeneities of the vertebral column.
Although a one-to-one comparison of porcine and human vertebrae was not possible due to differences in the number of thoracic vertebrae between the two species, the sizes and densities of porcine vertebrae at/near the treatment region were compared with vertebrae in the human lower thoracic spine to estimate the representativeness of the porcine model used here.
One posterior vertebral segment (T12-T15) and three individual vertebrae (T9-T11) were degassed for several days in a vacuum jar, until no air bubbles were observed. On the day of the imaging, samples were degassed for 3 h before imaging using an x-ray computed tomography (CT) scanner (Aquilon One, Toshiba Tec., Markham, ON, Canada). The vertebrae were aligned in the scanner, such that an axial plane across the vertebrae would be aligned with the axial plane of the scanner (i.e. as if they were in the body). Vertebrae were imaged with a resolution of 0.5 mm, so that they would be comparable to existing CT scans of ex vivo lower human thoracic vertebrae (T7-T12) previously used for bench and computational studies by our group .
The vertebrae were segmented using semi-automatic segmentation in ITK-SNAP  and 3D renderings of segmented data were visualized in MeshLab . CT scans and segmentation masks were imported into MATLAB to analyze vertebral density. As some tissue was left on the excised porcine vertebrae, the authors were concerned that some of this soft tissue would affect CT density analysis. Therefore, the top 5% of CT intensity voxels were considered to strictly isolate bone and to disregard water, air or soft tissue that may have been missed during segmentation.
To confirm that observed tissue effects, like BSCBO, were mechanical rather than thermal, 2D simulations were performed in k-Wave . The pstdElastic2D function was used to compute the elastic propagation of SBPK exposures (10 ms, 486 kHz, fixed pressure), in the dual aperture configuration, through the vertebral laminae (porcine T11) to the spinal canal. Medium densities were assigned using CT derived vertebral densities. Compressional and shear speeds of sound and attenuation coefficients were extrapolated from experimental data presented in  and . Following the acoustic simulations, the volume rate of heat deposition at each location in the simulation space was calculated based on the resultant pressures recorded in the time domain . This was used as input for kWaveDiffusion to compute a solution to Pennes' bioheat equation . Values of thermal conductivity and specific heat capacity were taken from , and absorption in the spinal cord was assumed to be the same as in the brain (5 Npm-1MHz-1 ). Thermal simulations were conducted over 5 min, with 10 ms heating every 1 s, to replicate the treatment scenario.
Blood spinal cord barrier opening (BSCBO)
In pigs 1 and 2, the cocktail of dexamethasone and meloxicam was found to restrict BSCBO. At locations treated with pulsed, sinusoidal exposures, hemorrhage was observed without EBD, as shown in Figure 5. This indicates that the BSCB was not substantially modified prior to the threshold for damage, or that the closure time following opening was very short and the barrier was no longer open at the time of EBD injection. These animals were excluded from further analysis and the remaining animals were only given diphenhydramine. These findings are discussed further in comparison with existing literature in the brain in the discussion section.
Macroscopic damage (haemorrhage) observed without blood spinal cord barrier opening in pigs given dexamethasone and meloxicam (pig 2).(Click on the image to enlarge.)
A summary of BSCBO and observed macroscopic damage at all treatment locations in pigs 3-8 is shown in Table 3. In pigs 3 and 4, EBD extravasation was observed for all treatments using 10 ms sinusoidal bursts. However, this was accompanied by extensive macroscopic damage, defined as observable hemorrhage on the surface of the cord. BSCBO observed using sinusoidal exposures in pig 4 is shown in Figure 6A. Nevertheless, this indicated that sufficient FUS could be delivered, through the intact spine, to achieve a therapeutic effect. In pig 4, EBD extravasation was also observed at one (1) location treated using SBPK exposures, which is indicated in Figure 6B. Here, BSCBO appeared more localized and there was no macroscopic damage observed. No effects were observed on contrast enhanced, T1-weighted GRE MRI. Pigs 3 and 4 were pilot animals, and were treated before a more robust and repeatable treatment protocol was established for pigs 5-8. In these animals, the treatments were very close together, sometimes overlapping, and consisted of multiple point sonications, making it difficult to distinguish EBD extravasation from different treatments. Therefore, the EBD extravasation reported in Table 3 for these animals is not location specific, and combines effects observed for each pulse type.
Blood spinal cord barrier opening using (A) pulsed sinusoidal exposures showing haemorrhage (pig 4) and (B) SBPK exposures (pig 4) confirmed by Evans blue dye (EBD) extravasation. (C,D,E) Blood spinal cord barrier opening in pig 8 confirmed by (C) EBD extravasation (left: posterior view, right: anterior view) and (D,E) adjacent coronal slices of post-treatment contrast enhanced T1-weighed MRI with the bottom rib labelled as an anatomical landmark. In (B) and (C), the arrows represent locations where EBD was observed. In (D) and (E), the arrows represent the locations at which gadolinium contrast enhancement was observed in any image slice (n=12). All scale bars are 1cm.(Click on the image to enlarge.)
Blood spinal cord barrier opening confirmed by Evans blue dye (EBD) extravasation in bisected spinal cord segments in one animal (pig 7). (A) shows the exterior of the cords (white matter) and (B) shows the interior of the cords (grey matter). The white arrows indicate the locations at which EBD extravasation was observed. All scale bars are 1cm.(Click on the image to enlarge.)
In pigs 5-8, which were treated with ramped pressure SBPK exposures, EBD extravasation was observed at 16/24 targeted locations. Some macroscopic damage was observed at three (3) of the locations with successful BSCBO in pig 8. An example from pig 8 is shown in Figure 6C, where 7/10 treatment locations had EBD extravasation. In this pig, although seven (7) BSCBO locations were confirmed using EBD extravasation, eight (8) locations were confirmed using post treatment contrast-enhanced T1-weighted FLAIR MRI (Figure 6D, E). The mean enhancement resulting from BSCBO in this animal was (31.8 ± 8.5 %) (21.7% - 48.9%) [(mean ± standard deviation) (minimum-maximum)].
In two (2) animals, pigs 5&6, spinal cords were bisected coronally. Qualitatively, the results showed more intense EBD extravasation in the grey matter of the spinal cord compared with the white matter (Figure 7).
Figure 8 shows representative histology examples of H&E stained histology images for the four histology grades: grade 0 (A&E), grade 1 (B&F), grade 2 (C&G), and grade 3 (D&H). Damage was more prominent in the grey matter compared with the white matter, with the exception of animals treated with 10 ms sinusoidal exposures where damage was widespread throughout the cord.
The spinal cords of pigs 6 and 7, which were bisected, were excluded from histological scoring. Due to the position of the cut, tissue was lost in the grey matter region, making it difficult to draw conclusions after processing.
Representative H&E stained histology images showing (A,E) grade 0 damage, (B,F) grade 1 damage, (C,G) grade 2 damage, and (D,H) grade 3 damage. (E-H) are 5x magnifications of (A-B). The black arrow in (F) indicates a small cluster of extravasated red blood cells.(Click on the image to enlarge.)
Summary of results for BSCBO, tissue damage and acoustic emissions
|Pig ID||Pulse Type||Location||Evans Blue Extravasation||MRI Enhancement||Macroscopic Damage||Histology Score||Subharmonic|
Acoustic emissions analysis
Using ramped pressure exposures, during treatments, a change in the pressure based on a detected subharmonic was never achieved. The method of Fourier analysis used in real-time was described in . There was one exception, at location 2 in pig 7, where a pressure drop was triggered at 46 s due to a false positive arising from a signal disruption during baseline measurements.
However, post-hoc analysis of the acoustic data showed that performing a subtraction of baseline data from treatment data in the time domain, before Fourier analysis, rather than performing a magnitude subtraction in the frequency domain, allowed for detection of the subharmonic (243 kHz), in most cases the 2nd harmonic (972 kHz) and in some cases the 1st ultraharmonic (729 kHz) using the 250 kHz PZT receiver. Acoustic data were available for pigs 4-8, with the exception of location 1 in pig 7, where the receiver experienced a technical failure.
Using this method, the subharmonic was detected for all treatments in pig 4 (sinusoidal and SBPK exposures). For ramped exposures, a change in the subharmonic was defined as an increase in the summation over a 40 kHz band centered on the frequency of interest of more than five (5) standard deviations above the mean of the first 10 sonications. This metric was chosen over two (2) standard deviations as it was determined empirically to decrease the likelihood detecting outliers in the data. Using two (2) standard deviations, false positives were detected in 39% of treatments. Changes in the subharmonic were observed for 20/23 locations treated with ramped exposures and viable acoustic data. These changes were observed in the range 1.9-2.1 MPa (non-derated), between 15 s and 143 s. Interestingly, the subharmonic was detected at four (4) locations where BSCBO was not confirmed. Figure 9 shows the pressure ramp (A) and changes in the subharmonic (B), the 2nd harmonic (C), and the 1st ultraharmonic (D). Figure 9E shows the maximum intensity frequency spectra at relevant time points: before subharmonic detection (10 s), initial detection of subharmonic (15 s), and a time point well after the detection of the subharmonic (50 s). A summary of the detection of the subharmonic at all treatment locations with available acoustic data is shown in Table 3.
Plots showing (A) non-derated pressures during ramped SBPK sonication, (B) changes in the FFT amplitude at the subharmonic (a jump in the subharmonic at 15 s is indicated by the red arrow), (C) changes in the FFT amplitude at the 2nd harmonic, and (D) changes in the FFT amplitude at the ultraharmonic. (E) shows maximum intensity projection frequency spectra at relevant time points. (B-E) correspond to location 2 in pig 8.(Click on the image to enlarge.)
CT-derived 3D renderings of (A) the sagittal view and (B) the coronal view of the posterior elements of the porcine vertebral column. (C) and (D) show % transmission within a 6mmx6mm field of view and at the focus location compared with a water case, respectively.(Click on the image to enlarge.)
CT derived vertebral dimensions
|Vertebral dimensions [mm]|
|Spinal canal depth||Spinal canal width|
FUS transmission through bone
CT-derived 3D renderings of the posterior elements of the porcine vertebral column in the lower thoracic region are shown in Figure 10A and B. Benchtop experiments through the posterior of four (4) vertebrae in the sonicated region at 69 locations, across four (4) spine samples, indicated a mean transmission to the target of (47.3 ± 7.0 %) (31.7%-61.9%) [(mean ± standard deviation) (minimum-maximum)]. However, transmission within a 6 × 6 mm2 field of view in three (3) perpendicular planes was (67.6 ± 12.1 %) (48.5%-95.0%). The mean focal shift was (2.7 ± 0.7) mm (0.8 mm - 3.0 mm). Examples of transmission to the target and within the 6 × 6 mm2 field of view are shown in Figure 10D and C respectively. The results show that % transmission is highly location dependent, with close to 100% transmission within a 6 × 6 mm2 when targeting near an acoustic window. It is likely that pressures could be further derated due to intervening muscle and additional connective tissues not taken into account in these measurements. Additionally, in the experimental set up, pigs were slightly in extension due to lying supine, so acoustic windows may have been more narrow than in the benchtop experiments.
Comparison of vertebral geometry in pigs and humans
CT-derived 3D renderings of the 10th human thoracic vertebra (T10) and the 11th porcine thoracic vertebra (T11) are shown in Figure 11. Measurements of spinal canal depth and width measured in porcine samples and human samples are shown in Table 4. On average, the spinal canal depths of the measured porcine vertebrae were (58 ± 4 %) of the spinal canal depths measured in the lower thoracic region of the human spine, while the spinal canal widths were (85 ± 6 %) of the spinal canal widths measured in the lower thoracic region of the human spine. The errors in Table 4 are the standard deviations of measurements across 20-38 CT slices.
The values of the CT derived density for the top 5% of voxels in each vertebra after segmentation are shown in Table 5. These values were computed separately for the vertebral bodies and for the posterior elements of the vertebrae. In the vertebral bodies of the lower thoracic spine, the porcine densities were on average (90 ± 4 %) of the human densities. In the posterior elements of the lower thoracic spine, the porcine densities were on average (70 ± 2 %) of the human densities.
Simulation results showed that at the maximum pressure used for ramped SBPK exposures, 2.1 MPa, the corresponding temperature rise in the spinal canal would be in the range 0.07 °C - 0.33 °C (assuming transmission through vertebrae of 48.5% - 95.0%). With MBs present, increased heating by a factor of ~3.6 can be expected . This corresponds to a temperature rise between 0.25 °C and 1.19 °C over the 5 min treatment duration. These temperatures are unlikely to result in thermally induced blood-spinal cord barrier opening .
CT derived densities of porcine and human vertebrae using the top 5% of CT voxels for each vertebra
|CT derived density [kgm-3]|
|Vertebral Body||Posterior elements|
CT-derived 3D renderings of (A) the top view and (B) the side view of the 10th human thoracic vertebra (T10), and CT-derived 3D renderings of (C) the top view and (D) the side view of the 11th porcine thoracic vertebra. (E) and (F) are axial slices showing the CT derived densities of the 10th human thoracic vertebra and the 11th porcine thoracic vertebra respectively.(Click on the image to enlarge.)
In this body of work, we have presented a porcine model of BSCBO through the intact spine, using SBPK FUS + MBs. Successful modification of the BSCB, as confirmed by the extravasation of EBD, and benchtop measurements of transmission through the vertebral column, indicate that minimally invasive (i.e. without laminectomy) delivery of FUS to the spinal cord is feasible.
BSCBO was confirmed by the extravasation of EBD using 10 ms sinusoidal pulses and 10 ms SBPK pulse trains. This study was not designed to evaluate the differences between these two pulse types. The treatment pressures used for sinusoidal (1.0 - 4.0 MPa) and SBPK (1.8 - 2.1 MPa) exposures, and the treatment protocol used were not directly comparable, but relevant observations are discussed here. While it is difficult to comment on levels of opening and damage, due to differences in pressure, there were differences observed in the distribution of opening and damage throughout the cord with the different pulse types. This is especially relevant in pig 4, where both pulse types were used with the same target spacing (Figure 6 A&B). Using sinusoidal exposures, widespread hemorrhage was observed on the surface of the cord in the treatment region. Upon histological scoring, extensive (grade 3) damage was observed throughout the cord on all histology levels. SBPK exposures resulted in BSCBO that was qualitatively more localized than long burst exposures. Further, hemorrhage on the surface of the cord was not observed in most cases. In the cases (3/24 locations treated with ramped SBPK exposures) where macroscopic damage was observed, it was qualitatively less prominent than in the sinusoidal cases. At locations treated with SBPK FUS, the most substantial damage observed through histological scoring was often observed at the center of the cord in the grey matter. The authors hypothesize that these differences could be explained, at least in part, by the differences in focal uniformity between the pulse types in the dual aperture, cross-beam configuration and the reduced potential for the formation of standing waves using SBPK pulse trains that was observed in a study using ex vivo human vertebrae . However, further experimental confirmation is required.
Another observation of this study was that when BSCBO was achieved, EBD extravasation at the center of the cord in the grey matter was more prominent than in the white matter. This effect has previously been reported in a study of BSCBO in the rabbit spinal cord using unfocused ultrasound, following laminectomies , and also in the brain in non-human primates . Although the spinal cords of two (2) animals were sectioned to assess this effect, sectioning was found to compromise histological processing and scoring, so it was not done for other animals. It is therefore possible, that treatment effects confined to the grey matter of the cord could be missed when assessing using EBD extravasation. In fact, in pig 8, where MRI enhancement was observed and quantified, there was one treatment location at which BSCBO was confirmed by MRI (enhancement = 24%), but not by EBD extravasation. This could mean that opening was localized in the grey matter. The differences observed throughout this study between effects observed in the grey and white matter of the spinal cord are likely due to differences in vascularization. The grey matter is supplied by a dense network of capillaries, while the white matter is poorly supplied . An additional explanation for the location in pig 8 that showed BSCBO on MRI but not by EBD extravasation is the comparative size of the tracers. Gadovist, the MRI contrast agent used, has a molecular weight of 604.7 Da , while serum albumin, to which EBD binds, has a molecular weight of 66.5 kDa . This implies that EBD could be less sensitive to the detection of limited BSCBO compared with contrast enhanced T1-weighted MRI, which is a limitation of the results presented here.
Differences in the time between treatment and administration of tracers (EBD and gadolinium) were not taken into account in animals that received multiple treatments. Because these differences could affect the results observing BSCBO, quantitative comparisons of opening are not presented here. The maximum time between the FUS treatment and EBD administration was ~5 hr (pig 8, location 1). For the last treated location, this time was ~1 hr (pigs 1-6) or immediate (pigs 7&8), depending on whether post treatment MRI was performed before or after EBD administration. Studies in the brain indicate that increased permeability can persist for several hours to days after the treatment depending on factors, including the magnitude of initial opening [4,53,54]. This is a further limitation of this study, because, for animals with many target locations, minimal opening occurring at one of the early target locations may have been missed using the current methods.
Definity MBs used during treatments are lipid encapsulated microspheres. Early in the study, in order to minimize the potential for an allergic reaction to liposomes that has been reported in pigs [38-40], animals were given a cocktail of dexamethasone, meloxicam and diphenhydramine. Prior research in the rat brain has shown that post-treatment administration of dexamethasone can help reduce the permeability of the blood-brain barrier after FUS-induced barrier opening and reduce the risk for tissue damage resulting from inflammation . In that study, rats were administered dexamethasone or saline 35 min and 24 h post FUS treatments. Using dynamic, contrast enhanced MRI, the reduction in permeability of the barrier at the 2 h time point compared with the 15 min time point was shown to be greater in the dexamethasone group than in the saline group. In our study, the spinal cords of animals that were administered dexamethasone prior to the treatment had haemorrhage without the observable extravasation of EBD. We hypothesize two possible explanations. Firstly, since dexamethasone was administered before FUS treatments, it may have preserved the integrity of the BSCB, such that opening was not achieved before the threshold for damage was reached. Alternately, due to the time required for treatment of multiple locations and post-treatment imaging, the time between FUS delivery to the final treatment location and EBD administration was >1 h in the animals who received dexamethasone. This could mean that if BSCBO was achieved, dexamethasone may have led to expedited restoration of the barrier in the time between treatment and EBD administration.
During treatments, attempts to leverage the acoustic emissions to control treatment exposures were unsuccessful. In post-treatment analysis of received acoustic signals, changes at the 2nd harmonic, subharmonic and 1st ultraharmonic frequencies were observed. However, changes at the frequency of interest, the subharmonic, were observed at the majority of locations treated, even at locations at which BSCBO was not confirmed. There were three (3) locations where the subharmonic was not observed. BSCBO was also not observed at these locations. These results could be explained by the following reasons. Firstly, the pressures used in this study are much higher than those used in previous studies of BSCBO [24,26]. This statement is true even when considering maximum transmission losses through the porcine spine measured in benchtop experiments. It is possible that, because of this overexposure, the detected subharmonic signals are indeed indicative of bubble events in the porcine spinal cord, and should have resulted in a drop in pressure using the controller. Alternatively, considering the limitations of a set up using a single acoustic receiver, the received acoustic signals cannot be localized to events in the spinal canal. Ex vivo experimental and simulation work from our lab suggests the potential for pre-focal effects resulting from reflections off the vertebral laminae, potentially with acoustic pressures that are higher than those achieved within the spinal canal . This explanation is supported by the observation of increased delivery of EBD in intervening tissue in some animals in this study. A better picture of bubble effects within the spinal cord could be provided by using large aperture phased arrays and passive acoustic mapping for receiving bubble signals, as has been done in brain studies [56-58]. Additionally, using a receiver with a central band that is not at the frequency of interest or a broadband receiver, could be useful for better detecting changes in acoustic signals.
Using SBPK FUS exposures, there were four (4) treatment locations at which BSCBO was achieved with very minor damage (grade 1) observed on histology. Inefficiencies in the transcardial perfusion technique at animal sacrifice meant that red blood cells were observed within vessels throughout the spinal cords, even outside of the treated regions. Depending on the orientation of blood vessels relative to the orientation of cutting for histology, it was difficult to distinguish intravascular clusters of red blood cells from grade 1 damage. Although grade 1 damage has been reported, inefficiencies in the transcardial perfusion technique may have led to the possible misclassification of grade 0 tissue. The understanding of tissue damage obtained in this study is also limited by the acute timepoint at which transcardial perfusion was done. It is possible that damage at locations graded 1 or 2 could be resolved at later timepoints as indicated by studies in the brain . This is an important result as it indicates that FUS-induced BSCBO may be achieved with minimal adverse effects for spinal cord tissue.
Benchtop testing of vertebral samples taken from animals after treatments revealed differences in vertebral size and density of pigs compared with humans. This analysis is limited as it compares one porcine spine with one human spine. Another limitation of this analysis is that it was performed ex vivo. While in vivo CT measurements would have been more relevant to the clinical case, ex vivo CT of human vertebrae and transmission measurements were readily available and this allowed for a more direct comparison. In the lower thoracic to upper lumbar region, pigs had a larger spinal canal width to depth ratio, with a spinal canal width of (58 ± 4)% and a spinal canal depth of (85 ± 6)% of samples in the human lower thoracic region. This geometric difference will affect how waves due to reflections within the vertebral canal interfere with each other. This decrease in symmetry could result in reduced potential for standing waves compared with humans. However, the smaller target within the porcine canal could lead to the opposite effect.
While the CT derived densities of porcine vertebral bodies in the lower thoracic region were (90 ± 4 %) of those in humans, densities in the posterior elements, including the laminae were (70 ± 2 %) of those in humans. This was an unexpected result, as vertebral densities in quadrupeds have been reported to be higher than humans, at least in the vertebral bodies . This discrepancy is most likely due to limitations placed on the weight of the pigs used in this study wherein in order to fit the animal and treatment platform within the MRI bore, they had not achieved maturation at the time of treatment. It is known that bone mineral density in growing animals' increases and reaches a peak at the point of maturation . The difference in bone geometry and density likely explains the higher levels of transmission through the pig vertebral laminae compared with humans that was observed. Over four (4) pigs, the mean transmission to the target measured on the bench was (47.3 ± 7.0 %) compared with a transmission of (31 ± 17 %) in humans  and (67 ± 15 %) in rats  at similar ultrasound frequencies. The authors hypothesize that the variability in transmission could be responsible for not observing BSCBO at some locations. Benchtop experiments also revealed the potential for pressure maxima occurring away from the intended focus, with a mean focal shift of (2.7 ± 0.7) mm (0.8 mm - 3.0 mm). This provides a possible explanation for the observed lack of uniformity in spacing of regions of EBD extravasation in some cases (Figure 6C).
In this study, control animals, without administered MBs, were not investigated. This control group would have been useful to distinguish whether the observed effects were due to low-power mechanical effects  or a high-power effect, like hyperthermia . However, the results of thermal simulations at the maximum pressures used (maximum temperature rise = 1.19 °C) and the low power levels associated with sparsely distributed SBPK exposures (maximum spatial peak temporal average intensity = 0.05 Wcm-2) provide convincing evidence that the thresholds for achieving thermally induced BSCBO would not have been met .
There are several limitations of this study and a range of challenges were encountered that should be addressed in future studies. Additional studies refining the treatment approach and examining chronic effects, including the impact on locomotor function, are needed. The authors propose several recommendations for future investigations of BSCBO in pigs or other large animals. Firstly, the inability to detect MRI enhancement, with the animal on the FUS system, using GRE sequences used to assess BBB opening was a major setback of this study. While the use of a FLAIR sequence together with placing animals on a spine coil gave better results, a spine coil that is compatible with the treatment system needs to be developed to permit accurate MRI assessment of opening during treatments. The development and implementation of a FUS-compatible spine coil will permit more robust and extensive MRI, including contrast-enhanced T1, T2 and T2* imaging to assess both BSCBO and toxicity. Secondly, a working controller to promote BSCBO while minimizing tissue damage is needed. In addition to the changes made in post-treatment analysis for this study, additional benchtop work is needed to develop an acoustic emissions based controller that is specialized for the application of SBPK pulses in the spinal cord. Greater receiver sensitivity is needed, and a receiver array to localize bubble events occurring in the spinal cord that offers the potential for passive acoustic mapping would also be advantageous. Finally, as evidenced by benchtop experiments, ultrasound transmission through the spine is location dependant and results in focal shifts on the order of several millimeters. This result reiterates the necessity for a transmit phased array to account for aberration as ultrasound transverses different paths through bone before arriving at the target within the spinal canal. A spine-specific phased array to address this concern is currently under development . A multi-element, phased transmit array would also allow for rapid electronic steering of the focus for treatment of diffuse disease.
This study presents the first evidence of FUS-induced BSCBO in a clinically relevant, large animal model through the intact spine. FUS was delivered using SBPK, which is a pulse scheme designed for use in the human spine to reduce standing waves and focal depth of field in a dual aperture configuration. Using SBPK exposures, at several locations BSCBO was observed with minimal tissue damage observed through histology, demonstrating the potential of this approach. During ramped pressure SBPK exposures, changes in acoustic signals from MBs were observed, although it is unclear whether these could be attributed to MBs within the spinal canal or in the intervening soft tissue. Future studies are needed to refine the treatment approach and assess chronic treatment effects. Despite the challenges and limitations of this study, this work represents an important step towards clinical translation of non-invasive FUS-induced BSCBO.
BBB: Blood-brain barrier; BBBO: Blood-brain barrier opening; BSCB: Blood-spinal cord barrier; BSCBO: Blood-spinal cord barrier opening; CNS: Central nervous system; CT: Computed tomography; EBD: Evans blue dye; FLAIR: Fluid-attenuated inversion recovery; FUS: Focused ultrasound; GRE: Gradient echo; H&E: Hematoxylin and eosin; IM: Intramuscular; IV: Intravascular; L1: 1st lumbar vertebra; MB: Microbubble; MRI: Magnetic resonance imaging; PI: Pulse inversion; PRF: Pulse repetition frequency; PVDF: Polyvinylidene difluoride; PZT: Lead zirconium titanate; SBPK: Short burst, phase keying; SNR: Signal-to-noise ratio; T12: 12th thoracic vertebra.
Support for this work was provided by the U.S. National Institute of Biomedical Imaging and Bioengineering under Grant R21EB023996, the Ontario Ministry of Research, Innovation and Science Early Researcher Award (ER17-13-159), and the Canada Research Chair Program.
The authors would like to formally acknowledge the following persons, without whom this work would not have possible. Firstly, the authors would like to thank Viva Chan, Ranjith Ramesh, and Shawna Rideout-Gros for veterinary care. They would like to thank E. Swanee Douglas, Yuexi Huang, PhD., and Ryan Jones, PhD. for experimental assistance. They also thank Jennifer Sun who processed tissue for histology and Rui Xu who provided CT data of human vertebrae.
The authors have declared that no competing interest exists.
1. Abbott NJ, Patabendige AAK, Dolman DEM, Yusof SR, Begley DJ. Structure and function of the blood-brain barrier. Neurobiol Dis. 2009;37:13-25
2. Bartanusz V, Jezova D, Alajajian B, Digicaylioglu M. The blood-spinal cord barrier: Morphology and clinical implications. Ann Neurol. 2011;70:194-206
3. Pardridge WM. Blood-brain barrier delivery. Drug Discov Today. 2007;12:54-61
4. Hynynen K, McDannold N, Vykhodtseva N, Jolesz FA. Noninvasive MR imaging-guided focal opening of the blood-brain barrier in rabbits. Radiology. 2001;220:640-6
5. Sheikov N, McDannold N, Vykhodtseva N, Jolesz F, Hynynen K. Cellular mechanisms of the blood-brain barrier opening induced by ultrasound in presence of microbubbles. Ultrasound Med Biol. 2004;30:979-89
6. McDannold N, Vykhodtseva N, Hynynen K. Targeted disruption of the blood-brain barrier with focused ultrasound: Association with cavitation activity. Phys Med Biol. 2006;51:793-807
7. Tung Y-S, Vlachos F, Choi JJ, Deffieux T, Selert K, Konofagou EE. In vivo transcranial cavitation threshold detection during ultrasound-induced blood-brain barrier opening in mice. Phys Med Biol. 2010;55:6141-55
8. O'Reilly MA, Hynynen K. Blood-brain barrier: Real-time feedback-controlled focused ultrasound disruption by using an acoustic emissions-based controller. Radiology. 2012;263:96-106
9. Sun T, Zhang Y, Power C. et al. Closed-loop control of targeted ultrasound drug delivery across the blood-brain/tumor barriers in a rat glioma model. Proc Natl Acad Sci. 2017;114:E10281-90
10. Tsai C-H, Zhang J-W, Liao Y-Y, Liu H-L. Real-time monitoring of focused ultrasound blood-brain barrier opening via subharmonic acoustic emission detection: Implementation of confocal dual-frequency piezoelectric transducers. Phys Med Biol. 2016;61:2926
11. McDannold N, Arvanitis CD, Vykhodtseva N, Livingstone MS. Temporary disruption of the blood-brain barrier by use of ultrasound and microbubbles: Safety and efficacy evaluation in rhesus macaques. Cancer Res. 2012;72:3652-66
12. Arvanitis CD, Livingstone MS, Vykhodtseva N, McDannold N. Controlled ultrasound-induced blood-brain barrier disruption using passive acoustic emissions monitoring. PLoS One. 2012;7:e45783
13. Aryal M, Vykhodtseva N, Zhang Y-Z, Park J, McDannold N. Multiple treatments with liposomal doxorubicin and ultrasound- induced disruption of blood-tumor and blood-brain barriers improves outcomes in a rat glioma model. J Control Release. 2013;169:103-11
14. Jordão JF, Ayala-Grosso CA, Markham K. et al. Antibodies targeted to the brain with image-guided focused ultrasound reduces amyloid-β plaque load in the TgCRND8 mouse model of Alzheimer's disease. PLoS One. 2010;5:e10549
15. Hsu P-H, Wei K-C, Huang C-Y. et al. Noninvasive and targeted gene delivery into the brain using microbubble-facilitated focused ultrasound. Ulasov I, Ed. PLoS One. 2013;8:e57682
16. Alkins R, Burgess A, Kerbel R, Wels WS, Hynynen K. Early treatment of HER2-amplified brain tumors with targeted NK-92 cells and focused ultrasound improves survival. Neuro Oncol. 2016;18:974-81
17. Hsu P-H, Lin Y-T, Chung Y-H. et al. Focused ultrasound-induced blood-brain barrier opening enhances GSK-3 inhibitor delivery for amyloid-beta plaque reduction. Sci Rep. 2018;8:12882
18. Karakatsani ME, Wang S, Samiotaki G. et al. Amelioration of the nigrostriatal pathway facilitated by ultrasound-mediated neurotrophic delivery in early Parkinson's disease. J Control Release. 2019;303:289-301
19. Mead BP, Mastorakos P, Suk JS, Klibanov AL, Hanes J, Price RJ. Targeted gene transfer to the brain via the delivery of brain-penetrating DNA nanoparticles with focused ultrasound. J Control Release. 2016;223:109-17
20. Mainprize T, Lipsman N, Huang Y. et al. Blood-brain barrier opening in primary brain tumors with non-invasive MR-guided focused ultrasound: A clinical safety and feasibility study. Sci Rep. 2019;9:321
21. Lipsman N, Meng Y, Bethune AJ. et al. Blood-brain barrier opening in Alzheimer's disease using MR-guided focused ultrasound. Nat Commun. 2018;9:2336
22. Weber-Adrian D, Thevenot E, O'Reilly MA. et al. Gene delivery to the spinal cord using MRI-guided focused ultrasound. Gene Ther. 2015;22:568-77
23. Payne AH, Hawryluk GW, Anzai Y. et al. Magnetic resonance imaging-guided focused ultrasound to increase localized blood-spinal cord barrier permeability. Neural Regen Res. 2017;12:2045-9
24. O'Reilly MA, Chinnery T, Yee M. et al. Preliminary investigation of focused ultrasound-facilitated drug delivery for the treatment of leptomeningeal metastases. Sci Rep. 2018;8:1-8
25. Wachsmuth J, Chopra R, Hynynen K. Feasibility of transient image-guided blood-spinal cord barrier disruption. AIP Conf Proc. 2009;1113:256-9
26. Fletcher S-MP, Ogrodnik N, O'Reilly MA. Enhanced detection of bubble emissions through the intact spine for monitoring ultrasound-mediated blood-spinal cord barrier opening. IEEE Trans Biomed Eng. 2019;67(5):1387-1396
27. Montero A-S, Bielle F, Goldwirt L. et al. Ultrasound-induced blood-spinal cord barrier opening in rabbits. Ultrasound Med Biol. 2019;45:2417-26
28. LeRhun E, Galanis E. Leptomeningeal Metastases of Solid Cancer. Curr Opin Neurol. 2016;29:797-805
29. Auricchio F, Scavone C, Cimmaruta D. et al. Drugs approved for the treatment of multiple sclerosis: review of their safety profile. Expert Opin Drug Saf. 2017;16:1359-71
30. Zufiría M, Gil-Bea FJ, Fernández-Torró R. et al. ALS: A bucket of genes, environment, metabolism and unknown ingredients. Prog Neurobiol. 2016;142:104-29
31. Xu R, O'Reilly MA. A spine-specific phased array for transvertebral ultrasound therapy: Design and simulation. IEEE Trans Biomed Eng. 2020;67:256-67
32. Xu R, O'Reilly MA. Simulating transvertebral ultrasound propagation with a multi-layered ray acoustics model. Phys Med Biol. 2018;63:145017
33. Pichardo S, Sin VW, Hynynen K. Multi-frequency characterization of the speed of sound and attenuation coefficient for longitudinal transmission of freshly excised human skulls. Phys Med Biol. 2011;56:219-50
34. Baron C, Aubry J-F, Tanter M, Meairs S, Fink M. Simulation of intracranial acoustic fields in clinical trials of sonothrombolysis. Ultrasound Med Biol. 2009;35:1148-58
35. Fletcher S-MP, O'Reilly MA. Analysis of multifrequency and phase keying strategies for focusing ultrasound to the human vertebral canal. IEEE Trans Ultrason Ferroelectr Freq Control. 2018;65:2322-31
36. Hope Simpson D, Ting Chin C, Burns PN. Pulse inversion doppler: A new method for detecting nonlinear echoes from microbubble contrast agents. IEEE Trans Ultrason Ferroelectr Freq Control. 1999;46:372-82
37. Busscher I, Ploegmakers JJW, Verkerke GJ, Veldhuizen AG. Comparative anatomical dimensions of the complete human and porcine spine. Eur Spine J. 2010;19:1104-14
38. Szebeni J, Fontana JL, Wassef NM. et al. Hemodynamic changes induced by liposomes and liposome-encapsulated hemoglobin in pigs: A model for pseudoallergic cardiopulmonary reactions to liposomes: Role of complement and inhibition by soluble CR1 and anti-C5a antibody. Circulation. 1999;99:2302-9
39. Szebeni J, Baranyi L, Savay S. et al. The role of complement activation in hypersensitivity to pegylated liposomal doxorubicin (Doxil). J Liposome Res. 2000;10:467-81
40. Szebeni J, Baranyi L, Savay S. et al. Liposome-induced pulmonary hypertension: properties and mechanism of a complement-mediated pseudoallergic reaction. Am J Physiol Hear Circ Physiol. 2000;279:H1319-28
41. Hynynen K, McDannold N, Sheikov NA, Jolesz FA, Vykhodtseva N. Local and reversible blood-brain barrier disruption by noninvasive focused ultrasound at frequencies suitable for trans-skull sonications. Neuroimage. 2005;24:12-20
42. Yushkevich PA, Piven J, Hazlett HC. et al. User-guided 3D active contour segmentation of anatomical structures: Significantly improved efficiency and reliability. Neuroimage. 2006;31:1116-28
43. Cignoni P, Callieri M, Corsini M, Dellepiane M, Ganovelli F, Ranzuglia G. MeshLab: an open-source mesh processing tool. In: Eurographics Italian Chapter Conference. 2008
44. Treeby BE, Cox BT. k-Wave: MATLAB toolbox for the simulation and reconstruction of photoacoustic wave fields. J Biomed Opt. 2010;15:021314-2 -021314-12
45. Pichardo S, Moreno-Hernández C, Drainville RA, Sin V, Curiel L, Hynynen K. A viscoelastic model for the prediction of transcranial ultrasound propagation: application for the estimation of shear acoustic properties in the human skull. Phys Med Biol. 2017;62:6938-62
46. Connor CW, Hynynen K. Patterns of thermal deposition in the skull during transcranial focused ultrasound surgery. IEEE Trans Biomed Eng. 2004;51:1693-706
47. Wissler EH. Pennes' 1948 paper revisited. J Appl Physiol. 1998;85:35-41
48. McDannold N, Vykhodtseva N, Hynynen K. Microbubble contrast agent with focused ultrasound to create brain lesions at low power levels: MR imaging and histologic study in rabbits. Radiology. 2006;241:95-106
49. McDannold N, Vykhodtseva N, Jolesz FA, Hynynen K. MRI investigation of the threshold for thermally induced blood-brain barrier disruption and brain tissue damage in the rabbit brain. Magn Reson Med. 2004;51:913-23
50. Tveten L. Spinal cord vascularity. III. The spinal cord arteries in man. Acta Radiol Diagnosis. 1976;17:257-73
51. National Center for Biotechnology Information. PubChem Database. Gadovist, CID=15814656. [cited 10 May 2020]. Available at:https://pubchem.ncbi.nlm.nih.gov/compound/Gadovist
52. PubMed Central. 5 Human Albumin. Transfus Med Hemotherapy. 2009;36:399-407
53. Samiotaki G, Konofagou EE. Dependence of the reversibility of focused-ultrasound-induced blood-brain barrier opening on pressure and pulse length in vivo. IEEE Trans Ultrason Ferroelectr Freq Control. 2013;60:2257-65
54. Sun T, Samiotaki G, Wang S, Acosta C, Chen CC, Konofagou EE. Acoustic cavitation-based monitoring of the reversibility and permeability of ultrasound-induced blood-brain barrier opening. Phys Med Biol. 2015;60:9079-94
55. McMahon D, Oakden W, Hynynen K. Investigating the effects of dexamethasone on blood-brain barrier permeability and inflammatory response following focused ultrasound and microbubble exposure. Theranostics. 2020;10:1604-18
56. Jones RM, O'Reilly MA, Hynynen K. Experimental demonstration of passive acoustic imaging in the human skull cavity using CT-based aberration corrections. Med Phys. 2015;42:4385-400
57. Jones RM, Deng L, Leung K, Mcmahon D, O'reilly MA, Hynynen K. Three-dimensional transcranial microbubble imaging for guiding volumetric ultrasound-mediated blood-brain barrier opening. Theranostics. 2018;8:2909-26
58. Arvanitis CD, McDannold N. Integrated ultrasound and magnetic resonance imaging for simultaneous temperature and cavitation monitoring during focused ultrasound therapies. Med Phys. 2013;40:112901
59. Smit TH. The use of a quadruped as an in vivo model for the study of the spine - biomechanical considerations. Eur Spine J. 2002;11:137-44
60. Inui A, Itamoto K, Takuma T. et al. Age-related changes of bone mineral density and microarchitecture in miniature pigs. J Vet Med Sci. 2004;66:599-609
61. Koivula M, Sevó N-Aimonen M-L, Strandén I. et al. Genetic (co)variances and breeding value estimation of Gompertz growth curve parameters in Finnish Yorkshire boars, gilts and barrows. J Anim Breed Genet 168-175. 2008;125:168-75
Corresponding author: E-mail: sfletcherutoronto.ca.