Vantage system

Manufactured by Verasonics

Sourced in United States

The Vantage system is a high-performance ultrasound research platform developed by Verasonics. It provides a flexible and customizable solution for advanced ultrasound imaging and research applications.

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Lab products found in correlation

Objet260 connex3, by Stratasys (1 mentions) Amira 2019, by Thermo Fisher Scientific (1 mentions) L7 4 probe, by Philips (1 mentions) Ie33 system, by Philips (1 mentions)

11 protocols using vantage system

High-resolution Cerebral Microvascular Imaging

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A 128 element, 15 MHz probe (Vermon) driven by Verasonics Vantage System was aligned to the coronal plane of the brain. The probe was moved along the anteroposterior axis by a step-by-step motor (0.1 mm step) to scan the whole cranial window (Fig. 1b). Each

μ

Doppler image was built from averaging 350 compound images. Tilted plane wave emission from four angles (− 6

^{\circ}

, − 2

^{\circ}

, 2

^{\circ}

and 6

^{\circ}

) were added coherently to form a compound image^{32 (link),33 (link)}. To increase the signal-to-noise ratio, each tilted plane wave was emitted three times and its backscattered echoes were automatically averaged in the Verasonics Vantage System memory (i.e. memory accumulation was set to three). All emission/reception times were adjusted to achieve a

μ

Doppler frame rate of 500 Hz. The lateral (i.e. probe’s pitch) and axial pixel resolution were 0.1 mm. The post-compounding dataset was arranged in an

N_{x}

\times

N_{z}

\times

N_{t}

matrix with

N_{x} = 128

(i.e. element number of the probe),

N_{z} = 92

and

N_{t} = 350

(number of compounded images).

Anzibar Fialho M., Vázquez Alberdi L., Martínez M., Calero M., Baranger J., Tanter M., Damián J.P., Negreira C., Rubido N., Kun A, & Brum J. (2022). Intensity distribution segmentation in ultrafast Doppler combined with scanning laser confocal microscopy for assessing vascular changes associated with ageing in murine hippocampi. Scientific Reports, 12, 6784.

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Imaging Posterior Segment of Eye

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The schematic diagram of our experimental setup for imaging the posterior segment of the eye is shown in Fig. 1. A L22–14v linear array probe (Verasonics Inc, Kirkland, WA, USA) operated by a high frequency Verasonics Vantage system (Verasonics Inc, Kirkland, WA, USA) was used. A ‘parametric’ transmit waveform at 15.625 MHz with a two-cycle pulse for each transmit angle was applied in this study. An angle step size of 2° was implemented in 12 angle compounding plane wave imaging with a post-compounded frame rate of 500 Hz. A total of 4 in-phase/quadrature (IQ) datasets were collected for each IOP, and each IQ dataset contained 2000 frames corresponding to 4 seconds of data acquisition. Thus, a total of 16 seconds of data were used to reconstruct the ULM image for each IOP level.
Before performing the experiment, we adjusted the transmit voltage from 5 V to 15 V (one-sided voltage) for the purpose of selecting the most suitable voltage to achieve a good MB visualization. Although the U.S FDA guidelines of acoustic intensity only apply to clinical use, we still tried to minimize the acoustic intensity in our study which could be a potential reference for future translational study. Therefore, the acoustic pressure output of the array transducer at the each transmit voltage was measured using a needle hydrophone (HGL-0085, ONDA Co, Sunnyvale, CA, USA) under the plane wave mode.

Qian X., Huang C., Li R., Song B.J., Tchelepi H., Shung K.K., Chen S., Humayun M.S, & Zhou Q. (2022). Super-resolution Ultrasound Localization Microscopy for Visualization of the Ocular Blood Flow. IEEE transactions on bio-medical engineering, 69(5), 1585-1594.

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Shear Wave Elastography Phantom Measurements

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A Verasonics Vantage system equipped with a C5-2v curved array transducer was used in this study (Verasonics, Inc., Kirkland, WA). For shear wave generation a single focused push beam with push duration of 600 μs was transmitted. The detection beams were wide beams with an f /9.9 focal configuration transmitted with a frequency of 2 MHz. Received signals from 2 steering angles were compounded [25 ], giving an effective pulse repetition frequency (PRF) of 2.77 kHz. For the phantom studies two sets of data were acquired, using 90 Volts for the transmitted push signal to achieve high signal-to-noise ratio (SNR) in the measurements and 20 Volts for the transmitted push to obtain measurements with low SNR. Measurements with SNR higher than 20 dB were considered high SNR and measurements with SNR lower than 10 dB were considered low SNR.

Amador C., Chen S., Manduca A., Greenleaf J.F, & Urban M.W. (2017). Improved shear wave group velocity estimation method based on spatiotemporal peak and thresholding motion search. IEEE transactions on ultrasonics, ferroelectrics, and frequency control, 64(4), 660-668.

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Dual-mode real-time imaging of kidney

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The performance of dual-mode real time imaging was also tested on the kidney of a healthy volunteer using a Verasonics Vantage system and a curved linear array transducer C1–6-D. This study was performed with IRB approval; the age of the male healthy volunteer was 31 year old. The healthy volunteer was recruited by the coordinator who explained the whole scanning process. The clinical data were then captured in an ultrasonic scanning room. The transmit frequency (4.16 MHz), sampling rate (16.67 MHz) and spatial resolution (0.45 mm) are identical to that in the phantom study. The start depth was set as 30 λ (~13.8 mm) and the end depths were set as 102 λ, 120 λ, and 138 λ for block sizes of 20×20, 25×25, or 30×30 pixels, respectively. In addition, these settings were used to evaluate the computational times of rSVD process with respect to the rank of tissue clutter subspace. The computational times of rSVD, beamforming, and image processing were evaluated by an MATLAB function tic/toc to measure the time required for a process. In addition, two methods, spatial correlation and lower order thresholding, were used for the estimation of the required threshold for the rank of tissue clutter subspace

Lok U.W., Song P., Trzasko J.D., Daigle R., Borisch E.A., Huang C., Gong P., Tang S., Ling W, & Chen S. (2020). Real time SVD-based clutter filtering using randomized singular value decomposition and spatial downsampling for micro-vessel imaging on a Verasonics ultrasound system. Ultrasonics, 107, 106163.

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Ultrasound Beam Characterization on Curved Phantoms

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The array was first tested on a flat surface, mounted within a 3D-printed (Stratasys Connex3 Objet260), water-tight testing apparatus. These initial tests confirmed the operation of the array by producing beam patterns. Beam steering and focusing were independently controlled by means of setting the delays on the graphical user interface of the MATLAB software controlling the Verasonics Vantage system. An Onda HGL-0200 hydrophone was used in conjunction with a motorised stage to sample the pressure in a grid along the x–z plane, with a grid resolution of 1 mm.
For the B-mode imaging of the curved gelatin phantoms, 85 g of uncoloured gelatin (Knox) were dissolved in 500 mL of boiling water before pouring this mixture into 3D-printed moulds of a pre-defined radius of curvature (in a range of R = 1–3 cm). After curing the moulds at 4 °C for 3 h, the gelatin phantoms were removed for testing. One set of moulds was always used as the bottom part—it was cast as a flat 5 cm by 5 cm by 2 cm block, with an air cavity located at the top center, with dimensions of 2 cm by 1 cm by 0.5 cm. In this way, the top half of the gelatin phantom could be easily changed out between measurements and offered an exact radius of curvature, while always measuring the same air pocket target. The FlexArray was manually wrapped around the curvature of the gelatin phantom to record each B-mode image.

Elloian J., Jadwiszczak J., Arslan V., Sherman J.D., Kessler D.O, & Shepard K.L. (2022). Flexible ultrasound transceiver array for non-invasive surface-conformable imaging enabled by geometric phase correction. Scientific Reports, 12, 16184.

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In Vivo Cerebral Blood Flow Imaging

Cited 1 time

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For µDoppler acquisition, the mouse was anesthetized with 120 mg/kg ketamine (Ventanarcol, Koing do Brasil Ltda., São Paulo, Brazil) and 16 mg/kg xylazine (Xylased*2, Vetcross) diluted in 300 µL of saline solution. Then, its head was shaved to avoid interference with the ultrasound signal caused by the air trapped inside the fur. A 128-element, 15 MHz ultrasound probe driven by Verasonics Vantage System was used for µDoppler imaging. To this end, each mouse was placed in a customized stereotaxic frame that allowed alignment of the ultrasound probe with the coronal plane of the brain. Each µDoppler image was generated by averaging 350 frames using a four-angle compound sequence and applying clutter filtering based on singular value decomposition (SVD) (Figure 1b). The cut-off values used in the SVD clutter filter were selected based on achieving on the best signal-to-noise ratio. Further information regarding this experimental procedure can be found in [48 (link)].

Martínez Barreiro M., Vázquez Alberdi L., De León L., Avellanal G., Duarte A., Anzibar Fialho M., Baranger J., Calero M., Rubido N., Tanter M., Negreira C., Brum J., Damián J.P, & Kun A. (2023). In Vivo Ultrafast Doppler Imaging Combined with Confocal Microscopy and Behavioral Approaches to Gain Insight into the Central Expression of Peripheral Neuropathy in Trembler-J Mice. Biology, 12(10), 1324.

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Simulated Ultrasound Imaging Deconvolution

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In simulation, ‘ground truth’ location of the image target was pre-defined, which allows us to compare it with the location reconstructed by image deconvolution based approach. The simulation mode of the same Verasonics Vantage system was used in this study where the attenuation is defined as − 0.5 dB/cm/MHz.
The system PSF at various depths were first simulated using single-point targets. Then, we simulated two-point targets to verify the image deconvolution approach. Figure 4 shows two-point targets at a depth of 6 mm (equal to the elevation focus of the array transducer). They are either separate by 100 μm in the axial direction or lateral direction, but kept at the same location in the other direction. Figure 5 (e–h) shows one two-point target laterally separated by 140 μm but at the same axial depth of 18 mm (maximum imaging depth for posterior pole of the rabbit eye). The axial or lateral separation distance was adjusted to take into account the calculated spatial resolution at each depth location to meet the Rayleigh criteria.

Qian X., Kang H., Li R., Lu G., Du Z., Shung K.K., Humayun M.S, & Zhou Q. (2020). In vivo Visualization of Eye Vasculature using Super-resolution Ultrasound Microvessel Imaging. IEEE transactions on bio-medical engineering, 67(10), 2870-2880.

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Realistic Tissue Motion Simulation

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To simulate realistic tissue motion, we used displacements estimated from sonographer hand motion phantom data to displace both the tissue and blood scatterers. Six volunteers acquired 0° plane wave channel data of a stationary quality assurance phantom (CIRS Model 040GSE, Norfolk, VA) using a 7.8125MHz center frequency at a pulse repetition frequency of 9kHz for 3s using a Verasonics Vantage System (Verasonics, Inc., Kirkland, WA) and L12–5 probe. A Hann apodization and aperture growth to achieve an F/# of 2 were implemented during receive beamforming. Beamformed data were band-pass filtered and up-sampled by a factor of 2 to achieve a sampling frequency of 62.5MHz. Total displacements over the first second of data were computed using the same method described in Section II-A using an axial kernel size of 1.25λ and a lag of 1ms for the relative displacement estimator. Total displacements were interpolated according to the location of the tissue and blood scatterers and used to generate 6 realistic tissue clutter realizations. Root mean square of hand motion velocities through slow-time are shown for each realization in Figure 2d. Velocities were computed on the hand motion data sets using a slow-time lag of 8ms and a kernel size of 1.25λ. Figure 2e shows a histogram of velocities for an example pixel from an example realization.

Tierney J., Walsh K., Griffith H., Baker J., Brown D, & Byram B. (2019). Combining Slow Flow Techniques with Adaptive Demodulation for Improved Perfusion Ultrasound Imaging without Contrast. IEEE transactions on ultrasonics, ferroelectrics, and frequency control, 66(5), 834-848.

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Biomechanical Biomarker Analysis via Shear Wave Techniques

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Two techniques were used to obtain mechanical elastic and viscoelastic biomarkers. The first, developed by our group, was TWE, and the other technique used a commercially available system for shear wave generation, a Verasonics Vantage system. The elasticity measurements using 2D SWEI and TWE may be expressed as either shear wave velocity (m/s) or shear moduli (kPa). The procedure for the samples scan is shown in Figure 1. Basically, it consists of preparing the samples (ex vivo liver and hydrogel phantoms) for testing; measuring them by generating torsional and shear waves; capturing the propagation of these waves; and, finally. analyzing the signal to reconstruct the biomechanical markers.

Faris I.H., Melchor J., Callejas A., Torres J, & Rus G. (2020). Viscoelastic Biomarkers of Ex Vivo Liver Samples via Torsional Wave Elastography. Diagnostics, 10(2), 111.

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Three-Point-Focus 3D Ocular Imaging

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Radio-frequency signals from the ultrasound 2D array were acquired and processed by the 256-channel Vantage system with an extended transmit upgrade (Verasonics, Inc., Kirkland, WA, USA). A customized three-point-focus line mode scan 3D imaging sequence (adapted from the algorithm packages in the Verasonics system) was developed to optimize the imaging quality, particularly for the surface and the bottom of the eyeball. The visualization of 3D reconstruction was conducted using Amira 2019 (Thermo Fisher Scientific, Waltham, MA, USA).

Lu G., Gong C., Sun Y., Qian X., Rajendran Nair D.S., Li R., Zeng Y., Ji J., Zhang J., Kang H., Jiang L., Chen J., Chang C.F., Thomas B.B., Humayun M.S, & Zhou Q. (2024). Noninvasive imaging-guided ultrasonic neurostimulation with arbitrary 2D patterns and its application for high-quality vision restoration. Nature Communications, 15, 4481.

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