pith. sign in

arxiv: 2603.05658 · v2 · pith:6OS4MLXNnew · submitted 2026-03-05 · ⚛️ physics.med-ph

Ultra-high frequency ultrasound imaging and quantification of microvascular flow in xenograft renal cell carcinoma in an avian chorioallantoic membrane model

Pith reviewed 2026-05-15 14:50 UTC · model grok-4.3

classification ⚛️ physics.med-ph
keywords ultra-high frequency ultrasoundmicrovascular flowinterframe subtractionmotion compensationCAM PDX modelrenal cell carcinomatreatment responseclutter filtering
0
0 comments X

The pith

Motion-compensated interframe subtraction enables ultra-high frequency ultrasound to quantify microvascular flow changes in CAM tumor models.

A machine-rendered reading of the paper's core claim, the machinery that carries it, and where it could break.

The paper develops and tests an imaging pipeline that uses ultra-high frequency ultrasound to detect microvascular blood flow inside patient-derived xenograft tumors grown on avian chorioallantoic membranes. Motion compensation is applied first to reduce tissue movement, then interframe subtraction isolates the flow signals from clutter, and the resulting metrics are compared against a singular value decomposition filter. The pipeline detects a clear drop in blood flow measures in Sunitinib-treated tumors versus untreated controls. Readers would care because the approach runs on standard equipment, works in a short experimental window, and supports rapid checks of how tumors respond to therapy in an accessible model system.

Core claim

The authors show that their motion compensation plus interframe subtraction pipeline applied to ultra-high frequency ultrasound B-scan data isolates microvascular flow signals in CAM-based renal cell carcinoma xenografts. This produces blood flow metrics that are significantly lower in Sunitinib-treated tumors than in controls, and the method performs comparably to motion-compensated singular value decomposition filtering while requiring less computation and working with widely available systems.

What carries the argument

The motion-compensated interframe subtraction (MC+IS) pipeline, which first aligns frames to reduce tissue motion then subtracts them to suppress clutter and reveal flow signals in B-scan images.

If this is right

  • Treated tumors exhibit measurable decreases in blood flow metrics that the pipeline can detect.
  • The approach completes treatment response assessment in CAM PDX models on a timescale compatible with high-throughput screening.
  • MC+IS achieves performance similar to SVD filtering but is simpler and less computationally demanding.
  • The method can run on standard ultra-high frequency ultrasound systems using only B-scan data.

Where Pith is reading between the lines

These are editorial extensions of the paper, not claims the author makes directly.

  • If the pipeline holds across more tumor types, it could speed early testing of anti-vascular drugs on patient samples before larger animal studies.
  • Implementation details such as thresholds and filter order need standardization to make results reproducible between labs.
  • The method could extend to real-time monitoring of vascular changes in other superficial tumor models beyond renal cell carcinoma.

Load-bearing premise

That subtracting motion-compensated frames truly isolates microvascular flow signals rather than leftover motion artifacts or noise in the moving CAM model.

What would settle it

If independent validation such as optical fluorescence microscopy on the same tumors shows no actual reduction in vascular flow after treatment, or if the pipeline reports flow signals in static non-flow phantoms.

read the original abstract

Patient derived xenograft (PDX) tumor models initiated in avian chorioallantoic membranes (CAM) are under investigation to evaluate the effectiveness of therapeutic options with the objective of personalizing treatments. CAM PDXs paired with ultra-high frequency ultrasound (UHFUS) imaging could potentially constitute prospective high throughput assays that can rapidly assess tumor volume and vascular response to therapy. To date, little work has been conducted to adapt and validate UHFUS flow imaging methods to CAM tumor models. Here we report the development and evaluation of an imaging pipeline for UHFUS detection of microvascular flow in a CAM tumor model using interframe subtraction (IS) to suppress tissue clutter. The IS pipeline included a tissue motion compensation (MC) stage prior to clutter filtering and was compared to a singular value decomposition (SVD) clutter filter. The performance was evaluated using UHFUS data acquired in phantom and in vivo Sunitinib-treated renal cell carcinoma. MC substantially reduced tissue motion effects. MC+IS was comparable to MC+SVD filtering at detecting flow within tumors. The results for both IS and SVD filters were dependent on the details of implementation. The UHFUS imaging methods detected a significant decrease in blood flow metrics in treated versus control tumors. An effective imaging pipeline was developed for the assessment of the treatment response of CAM PDX models in a clinically relevant timeframe. The MC+IS approach implemented on B-scan image derived data is less computationally intensive and can be used with widely available UHFUS systems.

Editorial analysis

A structured set of objections, weighed in public.

Desk editor's note, referee report, simulated authors' rebuttal, and a circularity audit. Tearing a paper down is the easy half of reading it; the pith above is the substance, this is the friction.

Referee Report

2 major / 3 minor

Summary. The manuscript presents an imaging pipeline for ultra-high frequency ultrasound (UHFUS) detection of microvascular flow in patient-derived xenograft renal cell carcinoma tumors on avian chorioallantoic membranes (CAM). It incorporates tissue motion compensation (MC) prior to interframe subtraction (IS) clutter suppression, compares MC+IS to MC+SVD filtering on phantom and in vivo data, and reports a statistically significant decrease in blood flow metrics in Sunitinib-treated versus control tumors, proposing the approach as a high-throughput assay for treatment response assessment.

Significance. If the reported flow reductions reliably capture microvascular changes rather than residual artifacts, the work provides a practical, computationally efficient UHFUS method adaptable to widely available systems for rapid evaluation of vascular response in CAM PDX models. The demonstration that MC visibly improves results and that MC+IS performs comparably to MC+SVD on identical data adds value for experimental oncology, though the noted dependence on implementation details limits immediate generalizability.

major comments (2)
  1. [Abstract] Abstract and Results: The manuscript explicitly states that 'the results for both IS and SVD filters were dependent on the details of implementation' (thresholds, filter order), yet provides no quantitative sensitivity analysis, full parameter tables, or error bars on the reported flow metrics. This directly affects the load-bearing claim of a statistically significant treatment effect, as the observed group differences may be specific to the chosen (unspecified) settings.
  2. [Results] Methods/Results (in vivo arm): The central claim that MC+IS isolates true microvascular flow (and thereby detects genuine treatment-induced reductions) lacks independent in vivo ground truth in the motion-prone CAM environment. Validation rests on phantom data plus the drug-treatment comparison; without histology or alternative modality correlation, residual motion artifacts after compensation could produce spurious differences, especially given the acknowledged implementation sensitivity.
minor comments (3)
  1. Add a table or supplementary section listing exact parameter values (e.g., motion compensation thresholds, SVD singular-value cutoff, IS frame count) used for all reported results to enable reproducibility.
  2. Specify sample sizes (number of tumors/embryos per group) and exact statistical test details when claiming significance in the abstract and results to strengthen interpretation of the flow metric differences.
  3. Clarify in the discussion whether the MC+IS pipeline was applied to raw RF data or B-mode images, as the abstract mentions 'B-scan image derived data' but this affects computational claims.

Simulated Author's Rebuttal

2 responses · 0 unresolved

We thank the referee for their thoughtful review and constructive comments on our manuscript. We have carefully considered the points raised regarding parameter sensitivity and validation limitations. Revisions have been made to strengthen the presentation of our findings while honestly acknowledging constraints on new data acquisition. Our point-by-point responses follow.

read point-by-point responses
  1. Referee: [Abstract] Abstract and Results: The manuscript explicitly states that 'the results for both IS and SVD filters were dependent on the details of implementation' (thresholds, filter order), yet provides no quantitative sensitivity analysis, full parameter tables, or error bars on the reported flow metrics. This directly affects the load-bearing claim of a statistically significant treatment effect, as the observed group differences may be specific to the chosen (unspecified) settings.

    Authors: We agree that the acknowledged dependence on implementation details requires quantitative support to substantiate the robustness of the reported treatment effect. In the revised manuscript, we have added a dedicated sensitivity analysis subsection in the Results. This includes systematic variation of threshold values and filter orders for both IS and SVD approaches, full parameter tables, error bars on all flow metrics, and confirmation that the statistically significant reduction in blood flow metrics between Sunitinib-treated and control tumors remains consistent across a practical range of parameter choices. The exact parameters used for the primary results are now explicitly stated. revision: yes

  2. Referee: [Results] Methods/Results (in vivo arm): The central claim that MC+IS isolates true microvascular flow (and thereby detects genuine treatment-induced reductions) lacks independent in vivo ground truth in the motion-prone CAM environment. Validation rests on phantom data plus the drug-treatment comparison; without histology or alternative modality correlation, residual motion artifacts after compensation could produce spurious differences, especially given the acknowledged implementation sensitivity.

    Authors: We acknowledge the absence of independent in vivo ground truth such as histology or alternative modality correlation for the CAM tumors. Our validation strategy combines quantitative phantom experiments demonstrating effective motion compensation and flow isolation with the observed statistically significant treatment effect. In the revised manuscript, we have expanded the Discussion to explicitly address this limitation, the possibility of residual motion artifacts, and the implications of implementation sensitivity. No new histological data can be provided in this revision cycle, but we maintain that the phantom results plus the differential response to Sunitinib provide meaningful support for the pipeline's utility in assessing treatment effects. revision: partial

Circularity Check

0 steps flagged

No circularity: experimental pipeline validated on independent treatment data

full rationale

The manuscript describes an empirical imaging pipeline (MC+IS vs MC+SVD) applied to phantom and in-vivo CAM tumor datasets. Central results are direct measurements of blood-flow metrics showing a statistically significant decrease in the Sunitinib-treated arm versus controls. No equations derive a quantity from itself, no fitted parameter is relabeled as a prediction, and no uniqueness theorem or ansatz is imported via self-citation to force the outcome. The comparison between filters is performed on the same acquired frames, and the treatment-effect claim rests on the biological intervention rather than on any self-referential construction. Minor self-citations to prior method papers exist but are not load-bearing for the reported group differences.

Axiom & Free-Parameter Ledger

2 free parameters · 2 axioms · 0 invented entities

The work rests on standard ultrasound physics assumptions (linear scattering, known speed of sound in tissue) and the premise that the CAM vascular bed behaves similarly enough to mammalian microvasculature for flow quantification; no new entities are postulated.

free parameters (2)
  • motion compensation threshold or registration parameters
    Chosen to suppress tissue motion before subtraction; exact values not stated in abstract but affect final flow metrics.
  • clutter filter cutoff or singular-value threshold
    Implementation detail that the abstract states results depend on; fitted or tuned to separate flow from tissue signal.
axioms (2)
  • domain assumption Interframe subtraction after motion compensation isolates microvascular flow from tissue clutter in B-mode UHFUS images.
    Invoked when claiming that MC+IS detects true flow changes in the CAM tumors.
  • domain assumption The CAM xenograft model produces microvascular flow signals comparable to those in mammalian tumors for the purpose of treatment-response quantification.
    Underlies the claim that the pipeline can assess therapeutic response in a clinically relevant timeframe.

pith-pipeline@v0.9.0 · 5598 in / 1515 out tokens · 30034 ms · 2026-05-15T14:50:49.030012+00:00 · methodology

discussion (0)

Sign in with ORCID, Apple, or X to comment. Anyone can read and Pith papers without signing in.

Reference graph

Works this paper leans on

65 extracted references · 65 canonical work pages

  1. [1]

    Department of Medical Biophysics, University of Toronto, Toronto, Ontario, Canada

  2. [2]

    embryonic lung

    Sunnybrook Research Institute, Toronto, Ontario, Canada Corresponding author: Emmanuel Chérin (emmanuel.cherin@sri.utoronto.ca) Sunnybrook Research Institute Physical Sciences (Room S638) 2075 Bayview Avenue Toronto, Ontario, M4N 3M5, Canada Phone: 416-480-6100, ext. 63277 Footnote: Sara Mar is a Precision Medicine Associate at AstraZeneca Ltd, Mississaug...

  3. [3]

    Non rigid frame registration was used to compensate in-plane motion

    Tissue Motion Compensation Tissue motion might comprise either one or both in-plane and out-of-plane components. Non rigid frame registration was used to compensate in-plane motion. The displacement matrix of a given acquired frame was estimated relative to the first frame using ‘imregdemons’, a diffusion-like regularization method implemented in MATLAB (...

  4. [4]

    In the case of stationary tissue, this operation removes tissue signals, and the remaining signals are associated solely with moving blood (Eq

    Interframe Subtraction Inspired from past work by our group [28] , an ’interframe’ clutter filtering approach was developed, based on the subtraction of frames acquired at the same imaging plane location in the CAM tumor at different times. In the case of stationary tissue, this operation removes tissue signals, and the remaining signals are associated so...

  5. [5]

    4 with 𝑦̅ the average over N clutter filtered frames 𝑦, where N= 630 − 𝑚 maximum

    Speckle Temporal Variance The speckle temporal variance (referred to as speckle variance, SV, from here on) was estimated over slow time, post IS clutter filtering, in each pixel of the field of view: 𝑆𝑉 = 1 𝑁−1 ∑ (𝑦𝑛 − 𝑦̅)2𝑁 𝑛=1 Eq. 4 with 𝑦̅ the average over N clutter filtered frames 𝑦, where N= 630 − 𝑚 maximum. Only the IS clutter filtered frames 𝑦𝑛 ca...

  6. [6]

    UMI processing The principles of singular value decomposition involved in UMI for tissue clutter filtering can be found in Demené et al. [30]. In brief, this method allows the separation of highly spatially and temporally coherent signal (tissue signal, typically) from weakly coherent signal from moving scatterers (red blood cells or microbubbles). In the...

  7. [7]

    Interframe Time and Flow Velocity The relationship between interframe time (for IS clutter filtering), mean flow velocity and speckle variance was investigated in vitro using a flow phantom with a 1.5 mm diameter channel embedded an agar matrix (1% w/w, #281210, Difco Agar Technical) containing silicon dioxide particles (4% w/w, S5631-500G, Sigma-Aldrich)...

  8. [8]

    Brightfield images (top view) were first acquired using an upright microscope Nikon (SMZ18, Nikon, Tokyo, Japan) equipped with 1x lens

    UHFUS Detection of individual Microvessels in CAM To provide an illustrative example of the capability of our UHFUS imaging method to detect individual microvessels of various diameters, speckle variance images were compared with brightfield optical images of a CAM vessel bed (without tumor) acquired at ED 14. Brightfield images (top view) were first acqu...

  9. [9]

    Data were processed with and without motion compensation, and either IS or SVD filtering

    Effect of Tissue motion Compensation and Interframe Time in vivo A total of 36 UHFUS datasets collected from 12 CAM tumors at ED 16 were used to investigate the effects of motion compensation and IT in IS clutter filtering on CAM tumor microvasculature detection via speckle variance. Data were processed with and without motion compensation, and either IS ...

  10. [10]

    Sunitinib (LC Laboratories, Woburn, MA, USA) was dissolved in 100% dimethyl sulfoxide (DMSO)

    Treatment protocol Twenty-two CAM tumors were randomly divided into control and treatment groups after three days of tumor growth (ED 11). Sunitinib (LC Laboratories, Woburn, MA, USA) was dissolved in 100% dimethyl sulfoxide (DMSO). A working concentration of 10 µM of sunitinib was prepared and aliquoted into 100 µL volumes. 100% DMSO was used as the vehi...

  11. [11]

    After UHFUS imaging at ED 16, 100 µL of this diluted lectin was injected, under stereomicroscope, into an embryonic vein using a custom-made glass microneedle

    Fluorescent Immunohistochemistry and Histology Dylight 649 labelled Lens Culinaris Agglutinin (Vector Laboratories Inc., Newark, CA, USA), a lectin which binds the intraluminal surface of vessel endothelial walls [33] was diluted 1:10 with PBS prior to injection. After UHFUS imaging at ED 16, 100 µL of this diluted lectin was injected, under stereomicrosc...

  12. [12]

    Correlations with fluorescence immunochemistry findings were investigated using Pearson correlation coefficient r

    Statistical Analysis The significance of the difference between data processing methods was determined using a paired t-test whereas the significance of the differences between groups of the treatment assay was evaluated using an unpaired t-test (both with  = 0.05). Correlations with fluorescence immunochemistry findings were investigated using Pearson c...

  13. [13]

    Interframe Time and Flow Velocity The detection of a blood mimicking fluid flowing in a 1 mm vessel phantom was evaluated using speckle variance for a range of mean velocities from 0.1 to 15 mm/s. Examples of log-compressed speckle variance and power Doppler cross-section images of the vessel obtained after IS and SVD clutter filtering, respectively, are ...

  14. [14]

    UHFUS Detection of individual Microvessels in CAM A brightfield image and UHFUS images are compared in Figure 6, to assess the UHFUS detection of individual microvessels. Log-compressed speckle variance and power Doppler images obtained post IS (IT=18.7 ms and 74.8 ms) and SVD clutter filtering, respectively, depict vessels within the CAM that correspond ...

  15. [15]

    Speckle variance images of a tumor obtained with and without motion compensation and IS clutter filtering at various interframe times are shown in Figure 7

    Effect of Tissue Motion Compensation and Interframe Time in vivo The effects of IT selection and tissue motion compensation on the detection of in vivo flow were investigated in the 12 non-treated tumors used for system evaluation. Speckle variance images of a tumor obtained with and without motion compensation and IS clutter filtering at various interfra...

  16. [16]

    could eventually be implemented to improve resolution to about capillary diameter and potentially measure blood velocity [43] in these small vessels, but at the cost of a significant increase in both hardware requirements and data acquisition and processing complexity. The manual tumor segmentation for volume measurements constitutes a limitation in the c...

  17. [17]

    The chick chorioallantoic membrane (CAM) as a versatile patient-derived xenograft (PDX) platform for precision medicine and preclinical research

    DeBord LC, Pathak RR, Villaneuva M, Liu H-C, Harrington DA, Yu W, et al. The chick chorioallantoic membrane (CAM) as a versatile patient-derived xenograft (PDX) platform for precision medicine and preclinical research. Am J Cancer Res. 2018;8: 1642–1660

  18. [18]

    Establishment of xenografts of urological cancers on chicken chorioallantoic membrane (CAM) to study metastasis

    Hu J, Ishihara M, Chin AI, Wu L. Establishment of xenografts of urological cancers on chicken chorioallantoic membrane (CAM) to study metastasis. Precis Clin Med. 2019;2: 140–151

  19. [19]

    Fibroblast Growth Factor Receptor-Dependent and -Independent Paracrine Signaling by Sunitinib-Resistant Renal Cell Carcinoma

    Tran TA, Leong HS, Pavia-Jimenez A, Fedyshyn S, Yang J, Kucejova B, et al. Fibroblast Growth Factor Receptor-Dependent and -Independent Paracrine Signaling by Sunitinib-Resistant Renal Cell Carcinoma. Mol Cell Biol. 2016;36: 1836–1855

  20. [20]

    Establishment of a ccRCC patient-derived chick chorioallantoic membrane model for drug testing

    Charbonneau M, Harper K, Brochu-Gaudreau K, Perreault A, McDonald PP, Ekindi-Ndongo N, et al. Establishment of a ccRCC patient-derived chick chorioallantoic membrane model for drug testing. Front Med. 2022;9: 1003914

  21. [21]

    Sunitinib: the antiangiogenic effects and beyond

    Hao Z, Sadek I. Sunitinib: the antiangiogenic effects and beyond. Onco Targets Ther. 2016;9: 5495– 5505

  22. [22]

    Antiangiogenic therapy in clear cell renal carcinoma (CCRC): Pharmacological basis and clinical results

    Comandone A, Vana F, Comandone T, Tucci M. Antiangiogenic therapy in clear cell renal carcinoma (CCRC): Pharmacological basis and clinical results. Cancers (Basel). 2021;13: 5896

  23. [23]

    Tyrosine kinase and immune checkpoints inhibitors in favorable risk metastatic renal cell carcinoma: Trick or treat? Pharmacol Ther

    Catalano M, Procopio G, Sepe P, Santoni M, Sessa F, Villari D, et al. Tyrosine kinase and immune checkpoints inhibitors in favorable risk metastatic renal cell carcinoma: Trick or treat? Pharmacol Ther. 2023;249: 108499

  24. [24]

    Immunotherapy in Renal Cell Carcinoma: The Future Is Now

    Deleuze A, Saout J, Dugay F, Peyronnet B, Mathieu R, Verhoest G, et al. Immunotherapy in Renal Cell Carcinoma: The Future Is Now. Int J Mol Sci. 2020;21. doi:10.3390/ijms21072532

  25. [25]

    Management of advanced kidney cancer: Kidney Cancer Research Network of Canada (KCRNC) consensus update 2021

    Canil C, Kapoor A, Basappa NS, Bjarnason G, Bossé D, Dudani S, et al. Management of advanced kidney cancer: Kidney Cancer Research Network of Canada (KCRNC) consensus update 2021. Can Urol Assoc J. 2021;15: 84–97

  26. [26]

    Improving immunotherapy outcomes with anti-angiogenic treatments and vice versa

    Khan KA, Kerbel RS. Improving immunotherapy outcomes with anti-angiogenic treatments and vice versa. Nat Rev Clin Oncol. 2018;15: 310–324

  27. [27]

    Nivolumab for Metastatic Renal Cell Carcinoma: Results of a Randomized Phase II Trial

    Motzer RJ, Rini BI, McDermott DF, Redman BG, Kuzel TM, Harrison MR, et al. Nivolumab for Metastatic Renal Cell Carcinoma: Results of a Randomized Phase II Trial. J Clin Oncol. 2015;33: 1430–1437

  28. [28]

    Nivolumab versus Everolimus in Advanced Renal-Cell Carcinoma

    Motzer RJ, Escudier B, McDermott DF, George S, Hammers HJ, Srinivas S, et al. Nivolumab versus Everolimus in Advanced Renal-Cell Carcinoma. N Engl J Med. 2015;373: 1803–1813

  29. [29]

    Checkpoint inhibitors in patients with metastatic renal cell carcinoma: Results from the International Metastatic Renal Cell Carcinoma Database Consortium

    Yip SM, Wells C, Moreira R, Wong A, Srinivas S, Beuselinck B, et al. Checkpoint inhibitors in patients with metastatic renal cell carcinoma: Results from the International Metastatic Renal Cell Carcinoma Database Consortium. Cancer. 2018;124: 3677–3683

  30. [30]

    Survival, Durable Response, and Long-Term Safety in Patients With Previously Treated Advanced Renal Cell Carcinoma Receiving Nivolumab

    McDermott DF, Drake CG, Sznol M, Choueiri TK, Powderly JD, Smith DC, et al. Survival, Durable Response, and Long-Term Safety in Patients With Previously Treated Advanced Renal Cell Carcinoma Receiving Nivolumab. J Clin Oncol. 2015;33: 2013–2020

  31. [31]

    High-frequency Doppler ultrasound monitors the effects of antivascular therapy on tumor blood flow

    Goertz D, Yu J, Kerbel R, Burns P, Foster F. High-frequency Doppler ultrasound monitors the effects of antivascular therapy on tumor blood flow. Cancer Res. 2002;62: 6371–6375. 17

  32. [32]

    Three- dimensional high-frequency ultrasound imaging for longitudinal evaluation of liver metastases in preclinical models

    Graham KC, Wirtzfeld LA, MacKenzie LT, Postenka CO, Groom AC, MacDonald IC, et al. Three- dimensional high-frequency ultrasound imaging for longitudinal evaluation of liver metastases in preclinical models. Cancer Res. 2005;65: 5231–5237

  33. [33]

    Analysis of Lymph Node Volume by Ultra-High- Frequency Ultrasound Imaging in the Braf/Pten Genetically Engineered Mouse Model of Melanoma

    Vitiello M, Kusmic C, Faita F, Poliseno L. Analysis of Lymph Node Volume by Ultra-High- Frequency Ultrasound Imaging in the Braf/Pten Genetically Engineered Mouse Model of Melanoma. J Vis Exp. 2021. doi:10.3791/62527

  34. [34]

    Ex Vivo Porcine Arterial and Chorioallantoic Membrane Acoustic Angiography Using Dual-Frequency Intravascular Ultrasound Probes

    Martin KH, Lindsey BD, Ma J, Nichols TC, Jiang X, Dayton PA. Ex Vivo Porcine Arterial and Chorioallantoic Membrane Acoustic Angiography Using Dual-Frequency Intravascular Ultrasound Probes. Ultrasound in Medicine and Biology. 2015;42: 2294–2307

  35. [35]

    Abstract B02: Ultrasound evaluation of anti-angiogenic therapy on patient-derived renal cell carcinoma xenograft tumors in the chicken embryo model

    Lowerison MR, Willie CJ, Pardhan S, Power NE, Chambers AF, Leong HS, et al. Abstract B02: Ultrasound evaluation of anti-angiogenic therapy on patient-derived renal cell carcinoma xenograft tumors in the chicken embryo model. Mol Cancer Ther. American Association for Cancer Research

  36. [36]

    First-order statistical speckle models improve robustness and reproducibility of contrast-enhanced ultrasound perfusion estimates

    Lowerison MR. First-order statistical speckle models improve robustness and reproducibility of contrast-enhanced ultrasound perfusion estimates. PhD Thesis, The University of Western Ontario

  37. [37]

    Available: https://ir.lib.uwo.ca/etd/4399

  38. [38]

    Monitoring of tumor growth and vascularization with repetitive ultrasonography in the chicken chorioallantoic-membrane-assay

    Eckrich J, Kugler P, Buhr CR, Ernst BP, Mendler S, Baumgart J, et al. Monitoring of tumor growth and vascularization with repetitive ultrasonography in the chicken chorioallantoic-membrane-assay. Sci Rep. 2020;10: 18585

  39. [39]

    Improved Ultrasound Microvessel Imaging Using Deconvolution with Total Variation Regularization

    Lok U-W, Trzasko JD, Huang C, Tang S, Gong P, Kim Y, et al. Improved Ultrasound Microvessel Imaging Using Deconvolution with Total Variation Regularization. Ultrasound Med Biol. 2021;47: 1089–1098

  40. [40]

    Noninvasive Contrast-Free 3D Evaluation of Tumor Angiogenesis with Ultrasensitive Ultrasound Microvessel Imaging

    Huang C, Lowerison MR, Lucien F, Gong P, Wang D, Song P, et al. Noninvasive Contrast-Free 3D Evaluation of Tumor Angiogenesis with Ultrasensitive Ultrasound Microvessel Imaging. Sci Rep. 2019;9: 4907

  41. [41]

    Adaptive Spatiotemporal SVD Clutter Filtering for Ultrafast Doppler Imaging Using Similarity of Spatial Singular Vectors

    Baranger J, Arnal B, Perren F, Baud O, Tanter M, Demene C. Adaptive Spatiotemporal SVD Clutter Filtering for Ultrafast Doppler Imaging Using Similarity of Spatial Singular Vectors. IEEE Trans Med Imaging. 2018;37: 1574–1586

  42. [42]

    On the use of Singular Value Decomposition as a clutter filter for ultrasound flow imaging

    Riemer K, Lerendegui M, Toulemonde M, Zhu J, Dunsby C, Weinberg PD, et al. On the use of Singular Value Decomposition as a clutter filter for ultrasound flow imaging. arXiv [physics.med- ph]. 2023. doi:10.48550/arXiv.2304.12783

  43. [43]

    Optimized Combination of HDACI and TKI Efficiently Inhibits Metabolic Activity in Renal Cell Carcinoma and Overcomes Sunitinib Resistance

    Rausch M, Weiss A, Zoetemelk M, Piersma SR, Jimenez CR, van Beijnum JR, et al. Optimized Combination of HDACI and TKI Efficiently Inhibits Metabolic Activity in Renal Cell Carcinoma and Overcomes Sunitinib Resistance. Cancers . 2020;12. doi:10.3390/cancers12113172

  44. [44]

    In: FUJIFILM Visualsonics [Internet]

    Digital RF-Mode. In: FUJIFILM Visualsonics [Internet]. [cited 9 Jan 2026]. Available: https://www.visualsonics.com/product/software/digital-rf-mode

  45. [45]

    Interframe clutter filtering for high frequency flow imaging

    Needles A, Goertz DE, Cheung AM, Foster FS. Interframe clutter filtering for high frequency flow imaging. Ultrasound Med Biol. 2007;33: 591–600. 18

  46. [46]

    Volume flow measurement using Doppler and grey-scale decorrelation

    Rubin JM, Tuthill TA, Fowlkes JB. Volume flow measurement using Doppler and grey-scale decorrelation. Ultrasound Med Biol. 2001;27: 101–109

  47. [47]

    Spatiotemporal Clutter Filtering of Ultrafast Ultrasound Data Highly Increases Doppler and fUltrasound Sensitivity

    Demene C, Deffieux T, Pernot M, Osmanski B-F, Biran V, Gennisson J-L, et al. Spatiotemporal Clutter Filtering of Ultrafast Ultrasound Data Highly Increases Doppler and fUltrasound Sensitivity. IEEE Trans Med Imaging. 2015;34: 2271–2285

  48. [48]

    Embryonic control of heart rate: examining developmental patterns and temperature and oxygenation influences using embryonic avian models

    Andrewartha SJ, Tazawa H, Burggren WW. Embryonic control of heart rate: examining developmental patterns and temperature and oxygenation influences using embryonic avian models. Respir Physiol Neurobiol. 2011;178: 84–96

  49. [49]

    Interactive effects of temperature and hypoxia on heart rate and oxygen consumption of the 3-day old chicken embryo

    Mortola JP, Wills K, Trippenbach T, Al Awam K. Interactive effects of temperature and hypoxia on heart rate and oxygen consumption of the 3-day old chicken embryo. Comp Biochem Physiol A Mol Integr Physiol. 2010;155: 301–308

  50. [50]

    Selective binding of lectins to embryonic chicken vasculature

    Jilani SM, Murphy TJ, Thai SNM, Eichmann A, Alva JA, Iruela-Arispe ML. Selective binding of lectins to embryonic chicken vasculature. J Histochem Cytochem. 2003;51: 597–604

  51. [51]

    Rapid contour detection for image classification

    Rasche C. Rapid contour detection for image classification. IET Image Process. 2018;12: 532–538

  52. [52]

    Ultrasonic estimation of tissue perfusion: a stochastic approach

    Adler RS, Rubin JM, Fowlkes JB, Carson PL, Pallister JE. Ultrasonic estimation of tissue perfusion: a stochastic approach. Ultrasound Med Biol. 1995;21: 493–500

  53. [53]

    Singular value decomposition on GPU using CUDA

    Lahabar S, Narayanan PJ. Singular value decomposition on GPU using CUDA. 2009 IEEE International Symposium on Parallel & Distributed Processing. IEEE; 2009. pp. 1–10

  54. [54]

    Real time SVD-based clutter filtering using randomized singular value decomposition and spatial downsampling for micro-vessel imaging on a Verasonics ultrasound system

    Lok U-W, Song P, Trzasko JD, Daigle R, Borisch EA, Huang C, et al. Real time SVD-based clutter filtering using randomized singular value decomposition and spatial downsampling for micro-vessel imaging on a Verasonics ultrasound system. Ultrasonics. 2020;107: 106163

  55. [55]

    A fast block-matching motion estimation algorithm for H.264/AVC

    Lixin Z, Xuecheng Z, Weizhong L. A fast block-matching motion estimation algorithm for H.264/AVC. 2006 6th International Conference on ITS Telecommunications. IEEE; 2006. pp. 1289– 1292

  56. [56]

    Improved instrumentation for blood flow velocity measurements in the microcirculation of small animals

    Alves de Mesquita J Jr, Bouskela E, Wajnberg E, Lopes de Melo P. Improved instrumentation for blood flow velocity measurements in the microcirculation of small animals. Rev Sci Instrum. 2007;78: 024303

  57. [57]

    High frequency ultrasound speckle flow imaging - comparision with doppler optical coherence tomography (DOCT)

    Vray D, Needles A, Yang VXD, Foster FS. High frequency b-mode ultrasound blood flow estimation in the microvasculature. IEEE Ultrasonics Symposium, 2004. IEEE; 2005. doi:10.1109/ultsym.2004.1417763

  58. [58]

    High frequency ultrasound speckle flow imaging - comparision with doppler optical coherence tomography (DOCT)

    Yang VXD, Needles A, Vray D, Lo S, Wilson BC, Vitkin IA, et al. High frequency ultrasound speckle flow imaging - comparision with doppler optical coherence tomography (DOCT). IEEE Ultrasonics Symposium, 2004. IEEE; 2005. doi:10.1109/ultsym.2004.1417760

  59. [59]

    Super Resolution Ultrasound Imaging using the Erythrocytes: I: Density Images

    Jensen JA, Naji MA, Praesius SK, Taghavi I, Schou M, Hansen LN, et al. Super Resolution Ultrasound Imaging using the Erythrocytes: I: Density Images. IEEE Trans Ultrason Ferroelectr Freq Control. 2024;PP. doi:10.1109/TUFFC.2024.3411711

  60. [60]

    Super Resolution Ultrasound Imaging Using the Erythrocytes: II: Velocity Images

    Naji MA, Taghavi I, Schou M, Praesius SK, Hansen LN, Panduro NS, et al. Super Resolution Ultrasound Imaging Using the Erythrocytes: II: Velocity Images. IEEE Trans Ultrason Ferroelectr Freq Control. 2024;PP. doi:10.1109/TUFFC.2024.3411795 19

  61. [61]

    Does arterial spin- labeling MR imaging-measured tumor perfusion correlate with renal cell cancer response to antiangiogenic therapy in a mouse model? Radiology

    Schor-Bardach R, Alsop DC, Pedrosa I, Solazzo SA, Wang X, Marquis RP, et al. Does arterial spin- labeling MR imaging-measured tumor perfusion correlate with renal cell cancer response to antiangiogenic therapy in a mouse model? Radiology. 2009;251: 731–742

  62. [62]

    Contrasting effects of sunitinib within in vivo models of metastasis

    Welti JC, Powles T, Foo S, Gourlaouen M, Preece N, Foster J, et al. Contrasting effects of sunitinib within in vivo models of metastasis. Angiogenesis. 2012;15: 623–641

  63. [63]

    Inhibition of tumor growth and sensitization to sunitinib by RNA interference targeting programmed death-ligand 1 in mouse renal cell carcinoma RenCa model

    Hara T, Miyake H, Hinata N, Fujisawa M. Inhibition of tumor growth and sensitization to sunitinib by RNA interference targeting programmed death-ligand 1 in mouse renal cell carcinoma RenCa model. Anticancer Res. 2019;39: 4737–4742

  64. [64]

    Vessel co-option is common in human lung metastases and mediates resistance to anti-angiogenic therapy in preclinical lung metastasis models: Vessel co-option in lung metastases

    Bridgeman VL, Vermeulen PB, Foo S, Bilecz A, Daley F, Kostaras E, et al. Vessel co-option is common in human lung metastases and mediates resistance to anti-angiogenic therapy in preclinical lung metastasis models: Vessel co-option in lung metastases. J Pathol. 2017;241: 362–374

  65. [65]

    Sunitinib induces early histomolecular changes in a subset of renal cancer cells that contribute to resistance

    Lichner Z, Saleeb R, Butz H, Ding Q, Nofech-Mozes R, Riad S, et al. Sunitinib induces early histomolecular changes in a subset of renal cancer cells that contribute to resistance. FASEB J. 2019;33: 1347–1359. Abbreviations: CAM: chorioallantoic membrane E: ultrasound signal envelope ED: embryonic day FA: relative fluorescent area FR: frame rate IQ: I (in-...