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Dynamic quantitative nonenhanced magnetic resonance angiography of the abdominal aorta and lower extremities using cine fast interrupted steady-state in combination with arterial spin labeling: a feasibility study
Journal of Cardiovascular Magnetic Resonance volume 21, Article number: 55 (2019)
Cine fast interrupted steady-state in combination with arterial spin labeling is a recently described nonenhanced magnetic resonance angiography (MRA) technique that relies on bolus tracking for time-resolved digital subtraction angiography-like displays of blood flow patterns. We evaluated the feasibility of applying this technique to display in-plane flow patterns in two regions: the abdominal aorta and lower extremity peripheral arteries.
We performed an institutional review board-approved study in healthy subjects and patients. In 7 healthy subjects, in-plane flow was imaged at 4 stations ranging from the lower legs to the aorto-iliac bifurcation (junction of the distal thigh and upper calf, mid-thigh, junction of the upper thigh and pelvis, upper pelvis). In 5 healthy subjects and 6 patients without abdominal aortopathy, images were acquired through the suprarenal abdominal aorta. Ten patients with known peripheral arterial disease and two patients with stable disease of the abdominal aorta were also evaluated. Peak velocity was compared at each of the 4 stations for cine fast interrupted steady-state in combination with arterial spin labeling and two-dimensional cine phase contrast in patients with normal vessels.
In-plane flow patterns were well visualized in all peripheral arterial stations and in the abdominal aorta, providing a high quality display of hemodynamic patterns along extensive lengths of the vessels. There was very strong positive correlation (r = 0.952, P < 0.05) and excellent agreement (intraclass correlation coefficient, 0.935; 95% confidence interval, 0.812–0.972) between peak flow velocities measured by cine fast interrupted steady-state in combination with arterial spin labeling and two-dimensional cine phase contrast. In 10 patients with peripheral artery disease and 2 patients with aortic pathology, cine fast interrupted steady-state in combination with arterial spin labeling provided a visual demonstration of abnormal hemodynamics.
This feasibility study suggests that cine fast interrupted steady-state in combination with arterial spin labeling provides an efficient, high quality and physiologically accurate display of in-plane flow patterns over extensive lengths of the lower extremity peripheral arteries, which can be difficult to achieve using other MRA techniques.
Peripheral artery disease (PAD) is a major health issue worldwide, affecting approximately 202 million people globally . Imaging evaluation for those under consideration for revascularization was traditionally performed using catheter-directed digital subtraction angiography (DSA) . In efforts to reduce the invasiveness and risk, physicians have turned to contrast-enhanced magnetic resonance angiography (CEMRA) and computed tomography angiography (CTA) for non-invasive vascular evaluation [3,4,5]. CTA is a static technique that provides little information about the hemodynamic status of the arteries, whereas time-resolved CEMRA can be used to provide a dynamic display of arterial flow patterns. However, time-resolved CEMRA has limited temporal resolution and primarily provides qualitative rather than quantitative evaluation of blood flow [6, 7]. Both CTA and time-resolved CEMRA require the administration of contrast agents, which may be contraindicated in patients with impaired renal function.
Cine fast interrupted steady-state in combination with arterial spin labeling (cFASL) is a recently-described nonenhanced MRA technique that provides a DSA-like display of in-plane flow patterns with high temporal resolution . Rather than measure phase shifts that have been created by the flow of arterial spins through magnetic field gradients, which is the underlying principle for phase contrast methods, cFASL quantifies flow velocity based on measuring the temporally-resolved displacement of a radiofrequency (RF)-labeled bolus of arterial spins. Unlike 2-dimensional phase contrast (2DPC), cFASL is insensitive to the effects of partial volume averaging and enables in-plane flow patterns to be directly visualized. We hypothesized that cFASL could be used to efficiently display arterial hemodynamics over extensive lengths of the aorta and lower extremity peripheral arteries.
This study was compliant with the Health Insurance Portability and Accountability Act. Four groups of subjects were studied. In the first group cFASL and 2DPC were acquired at four stations throughout the lower extremity arteries in 7 healthy subjects without a history of PAD (4 male, 25–55 years). In the second group, cFASL and 2DPC were acquired through the suprarenal segment of the abdominal aorta in 5 healthy subjects and 6 patients (5 male, 25–75 years) during a clinically-indicated magnetic resonance (MR) exam for pathology outside of the supra-renal aorta. A third group included 10 patients with known peripheral artery pathology (5 male, 46–81 years). A fourth group of 2 patients with disease of the abdominal aorta included one with a chronic type B dissection and one with arcuate ligament syndrome (1 male, 46–48 years). All patients provided written, informed consent except for patients in group 2, who had IRB-approved waiver of consent.
All studies were performed on a 1.5 T system (MAGNETOM Avanto, Siemens Healthineers, Erlangen, Germany) with a standard phased array body coil. No intravenous contrast was administered.
In the lower extremity patients and volunteers, standard localizer scans were followed by nonenhanced, electrocardiogram (ECG)-gated quiescent-interval slice-selective (QISS) MRA  to provide an anatomical roadmap of the lower-extremity peripheral arteries.
cFASL was used to measure peak flow velocities in healthy vessels and to portray flow patterns in both healthy and diseased arteries. In the first group, imaging in each subject was performed at 4 stations ranging from the lower legs to the aortic bifurcation (junction of the distal thigh and upper calf, mid-thigh, junction of the upper thigh and pelvis, upper pelvis) in a coronal and/or sagittal plane. Several slices were acquired at each station to ensure coverage of the entire thickness of the target vessels. For coronal imaging, 4 to 6 slices (9-mm, 10% overlap) were obtained at each station for bilateral arterial evaluation versus 3 to 4 slices for sagittal imaging (right leg only). In the second group, imaging was performed at a single station in the suprarenal abdominal aorta using 1–3 slices in the sagittal plane. In the third and fourth groups, cFASL was acquired in 1–6 slices in coronal, sagittal and/or axial planes. In some subjects, additional cFASL acquisitions were performed using a thick (e.g. 27-mm) slice to assess the impact of partial volume averaging on image quality.
Spin labeling was performed in all studies using a 10.24-ms duration adiabatic inversion RF pulse which was applied shortly after every second R-wave to inflowing arterial spins over a 25-mm thick region orthogonal to the vessel axis. This process resulted in the interleaved acquisition of labeled and unlabeled data, which helped to minimize misregistration artifact from patient motion. Background suppression was achieved by complex subtraction of the labeled and unlabeled cine images. Imaging parameters included 240 radial views with equidistant azimuthal view angle increment of ~ 15 degrees, 40 shots, sampling bandwidth = 888 Hz/pixel, TE ~ 1.5 ms, echo spacing ~ 3.0 ms, excitation flip angle ~ 60 degrees, prospective cine acquisition, 6 balanced steady-state free precession (bSSFP) repetitions per fast interrupted steady state (FISS) module, matrix 240 × 240 (sagittal) or 300 × 300 (coronal), 27 reconstructed cine phases (no view sharing) for an acquisition window of 500 ms, temporal resolution ~ 20 ms.
2D phase contrast
Through-plane 2DPC was performed immediately following cFASL at a single level within each station, with the slice oriented orthogonal to the artery in normal vessels. Based on empirical testing, the initial velocity encoding (VENC) values were 50 cm/s for calf-thigh, 80 cm/s for mid-thigh, 100 cm/s for thigh-pelvis, 120 cm/s for upper pelvis and 150 cm/s for the suprarenal aorta. In the event of aliasing, the VENC was increased by approximately 50% and the 2DPC acquisition was repeated. Other imaging parameters included TE 3.5–5 ms, repetition time 25–50 ms, matrix ~ 244 × 300 and a flip angle of ~ 10 degrees.
An ImageJ (National Institutes of Health and the Laboratory for Optical and Computational Instrumentation, University of Wisconsin, Madison, Wisconsin, USA) script was developed to semi-automate calculation of peak velocity from the cFASL in normal vessels. The cine images were uploaded and a maximum intensity projection (MIP) image was created including all the slices. A spline path was manually drawn along the course of the vessel and the program calculated the peak velocity based on frame-to-frame displacement of the bolus along the manually drawn vessel course and the time resolution between successive cine frames. Bolus arrival occurred when the signal intensity of the vessel exceeded the threshold value of S = μB + 2σB, where μB and σB are the mean and standard deviations of a nearby circular region of background signal (size ≈300mm2). Peak velocity on cFASL was computed as the maximal value of the distance of bolus travel in one frame divided by the time resolution of the frame. The peak velocities were calculated individually by two radiologists and any discrepancies were reviewed with agreement in consensus by two radiologists (E.A., R.R.E.). Peak velocities from through-plane 2DPC were calculated using Argus Flow (Siemens Healthineers).
Image quality analysis
Image quality for all normal and diseased cases was assessed individually by two radiologists (E.A. and R.R.E.) based on anonymized MIP images. Thirty-nine images of healthy subjects or normal patients were evaluated and 12 images of pathologic segments. The following 4-point scoring system was used: 1 = non-diagnostic, image quality inadequate for diagnosis; 2 = fair, image quality marginally acceptable for diagnosis; 3 = good, image quality adequate for confident diagnosis; and 4 = excellent, excellent image quality providing a highly-confident diagnosis.
The relationships between the measurements acquired in normal vessels using both 2DPC and cFASL were examined with the Pearson product-moment correlation coefficient analysis. Two-way mixed-effects single measures intra-class correlation coefficient (ICC) for absolute agreement was used to assess agreement between flow velocity measured on 2DPC and cFASL using IBM SPSS Statistics for Windows, version 22 (Statistical Package for the Social Sciences (SSPS) International Business Machines, Inc., Armonk, New York, USA). Agreement was also evaluated using the approach by Bland-Altman  by calculating the mean difference (μ) and standard deviation (SD) of the difference in flow velocity measurements between 2DPC and cFASL from all subjects and analysis planes. From these data, the 95% limits of agreement (μ ± 1.96SD) were calculated. For image quality, the mean score and standard deviation for each reviewer overall, in normal segments and in diseased segments was calculated.
Scan time for the cFASL sequence was approximately 65 s per slice. cFASL of each vessel segment was typically acquired in 1–6 slices depending on the location and plane of imaging, which gives an overall scan time of 65–390 s. For unilateral evaluation, sagittal cFASL was more efficient than coronal imaging as fewer slices were needed to encompass the arteries, whereas imaging in the coronal plane permitted direct comparison of flow between limbs. In one subject, 2DPC through the upper thigh was not evaluable due to susceptibility artifact, so neither 2DPC nor cFASL data at this level was included in the analysis. Post-processing time was rapid (approximately 1 to 2 min per level) for both 2DPC and cFASL.
Peak velocity measurements in Normal vessels overall
For cFASL peak velocity measurements in normal vessels, the mean, σ and range were 86.4, 26.5, 43.5–147.0 cm/s; for 2DPC, the mean, SD and range were 81.3, 25.4, 37.8–135.2 cm/s. Bland-Altman analysis of agreement of cFASL and 2DPC measurements at all levels revealed a mean velocity difference of 5.1 cm/s (SD= 7.8; 95% limits of agreement -10.8/21.0 cm/s) (Fig. 1a). 2DPC and cFASL peak velocity measurements were found to be in excellent agreement (ICC = 0.935, 95% confidence interval: 0.812–0.972, P < 0.001) and were also strongly correlated (r = 0.952, P < 0.001) (Fig. 2a).
cFASL velocity measurements in normal vessels overall including both the lower extremities and suprarenal aorta were greater than 2DPC at 28/38 (74%) individual levels with mean peak velocities of 86.5 cm/s and 81.4 cm/s respectively.
Peak velocity measurements healthy subjects lower extremities
For cFASL in the lower extremities including all levels, the mean, SD, and range of peak velocities were 87.3, 24.3, 45.5–136.3 cm/s; for 2DPC, the mean, SD, and range were 81.2, 23.4, 42.2–127.4 cm/s (Table 1). Bland-Altman analysis of agreement of cFASL and 2DPC measurements at all levels revealed a mean velocity difference of 6.1 cm/s (SD = 8.15; 95% limits of agreement -9.9/22.1 cm/s) (Fig. 1b). Peak velocity measurements acquired using both techniques were strongly correlated (r = 0.942, P < 0.001) (Fig. 2b). ICC showed excellent agreement overall and at each station individually, except in the proximal thigh where agreement was good (Table 2).
Peak velocity measurements patients – suprarenal aorta
For cFASL in the suprarenal aorta, the mean, SD and range were 84.6, 32.7, 43.5–147 cm/s; for 2DPC, the mean, SD and range were 81.9, 31.0, 37.8–135.2 cm/s (Table 3). Bland-Altman analysis of reproducibility of cFASL and 2DPC measurements at all levels revealed a mean velocity difference of 2.6 cm/s (SD = 7.8; 95% limits of agreement -12.6/17.9 cm/s) (Fig. 1c). Peak velocity measurements acquired using both techniques were found to be in excellent agreement (ICC = 0.970, 95% confidence interval: 0.897–0.992, P < 0.001) and were strongly correlated (r = 0.972, P < 0.001) (Fig. 2c).
Evaluation of flow patterns in healthy vessels and vascular pathology
Using cFASL, in-plane flow patterns were visualized in all evaluated peripheral arterial segments (Fig. 3) and in the abdominal aorta (Fig. 4). Additional movie files show this in more detail [see Additional files 1 and 2]. Hemodynamic effects of vascular pathology including dissection, stenosis and occlusion were also well depicted.
For instance, Fig. 5 demonstrates a focal stenosis of the origin of the right SFA (Patient 1). The stenosis was visually confirmed on cFASL and differential in-plane flow was noted between the right and left sides consistent with a hemodynamically-significant lesion. Additional movie files show this finding in more detail [see Additional file 3]. A hemodynamically-significant lesion was confirmed on 2DPC which measured peak velocities of 87.9, 158.2 and 66.8 cm/s proximal to, within, and distal to the stenosis.
Figure 8 is from a subject with a chronic type B aortic dissection extending from the thoracic aorta distally through the abdominal aorta and into the right common iliac artery (Patient 10). Maximum intensity projection of five coronal 9-mm slices using cFASL (Fig. 8b) displayed markedly different flow patterns in the true and false lumens. A single 27-mm cFASL slice provided a comparable display of flow patterns (Fig. 8c) to the multi-slice cFASL acquisition in a fraction of the scan time. Additional movie files show this finding in more detail [see Additional file 4].
Mean (± SD) overall, normal and diseased segment scores were 3.6 (±0.5), 3.7 (±0.5) and 3.2 (±0.4), respectively, for reader 1 and 3.4 (±0.7), 3.5 (±0.6) and 3.1 (±0.8), respectively, for reader 2. These results are compatible with overall good image quality in both normal and diseased segments, although image quality was slightly better in normal segments.
This preliminary study demonstrates that cFASL provides a physiologically accurate display of in-plane flow patterns over extensive lengths of the lower extremity peripheral arteries and abdominal aorta. The FISS readout which is key to this technique is a novel variant of the widely-used bSSFP pulse sequence. It combines a frequently-interrupted echo train with a radial k-space trajectory, while periodic application of gradient and radiofrequency spoiling suppresses flow artifacts from out-of-slice and off-resonant spins . FISS builds upon prior work using interrupted steady-state sequences, such as the S5FP technique . With this earlier technique, which utilized a Cartesian k-space trajectory, the frequent disruption of the steady-state signal could produce severe image artifacts. To avoid these artifacts, FISS uses a radial k-space trajectory with equidistant view angle increments. The benefit is decreased flow artifact and fat signal compared to traditional bSSFP, with greatly reduced flow saturation effects compared with fast low-angle shot (FLASH) . The combination of FISS with ASL was recently described to enable the visualization of in-plane flow patterns within the major arteries of the chest and abdomen . However, validation of cFASL for the measurement of in vivo flow velocities has not previously been described, nor has it been used to image vascular pathology involving the peripheral arteries or abdominal aorta.
In this study, both large and small vessels were evaluated with cFASL. In healthy subjects, the suprarenal abdominal aorta has a predominantly plug flow pattern whereas the smaller peripheral arteries have a predominantly laminar flow pattern . In individuals without significant arterial pathology, we found that peak velocity measurements using cFASL correlated well with 2DPC for both plug and laminar flow patterns. This finding suggests that cFASL may be applicable for flow measurements in both large and small arteries.
For qualitative evaluation, cFASL reliably depicted in-plane flow patterns in both healthy and diseased vessels. For instance, visual analysis of time-resolved cFASL images in PAD patientsreadily demonstrated acceleration of the labeled bolus through hemodynamically-significant stenoses along with differential rates of bolus progression versus healthy vessels in the contralateral limb. Tortuous progression of the labeled bolus through collateral vessels, swirling flow in aneurysms, as well as differential progression of the labeled bolus through the true and false lumens of an aortic dissection were also readily apparent. However, for quantitative evaluation of flow velocities in the setting of significant arterial pathology, cFASL has limitations since the labeled bolus must remain substantially intact and trackable over the measurement period. For instance, due to dispersion of the labeled bolus from turbulence, we found that the technique was not well suited for flow measurements across hemodynamically-significant stenoses.
Unlike 2DPC, cFASL is largely insensitive to partial volume averaging due to the extreme level of background signal suppression. For instance, a single 27-mm thick slice allowed the semi-projective depiction of arterial flow patterns through extensive lengths of an aortic dissection despite the small caliber of the true lumen. Using such thick slices, one can image substantial lengths of a peripheral artery using a single cine image series, enabling a several-fold reduction in exam time compared with the predominantly multi-slice approach used in the current study. However, further study is needed to determine whether the accuracy of the flow velocity measurements is maintained with thick slices.
2DPC has been used since the 1980s for evaluation of pulsatile flow in the body [14, 15] and has been validated and applied to the lower extremities since the 1990s [16,17,18]. While 2DPC allows accurate measurement of through-plane flow, considerations of scan time generally limit its use to a few slice locations. Moreover, it is suboptimal for imaging lower extremity arteries in a non-axial orientation due to partial volume averaging between flowing spins and stationary background tissue, which can cause erroneous velocity measurements.
We found that peak velocities measured by cFASL were consistently higher compared to 2DPC (at 28 of 38 stations). This discrepancy could be explained in part by the fact that, while 2DPC is a well-established technique for through-plane flow quantification [16,17,18], it has been shown to consistently underestimate velocities compared to Doppler ultrasound . Compared with 2DPC, 4D flow (i.e. 3D cine PC) would have provided a more accurate reference standard for flow quantitation. However, it was not used in the current study due to impractically long scan times (e.g. 10 to 15 min per station) and time-consuming image analysis . Despite the limitations of 2DPC, we found very strong positive correlation and excellent agreement between cFASL and 2DPC for the quantification of peak flow velocities throughout the peripheral arterial territory in healthy vessels.
There are several limitations with the cFASL technique. As with other bSSFP-based imaging techniques, the FISS readout is prone to artifacts from off-resonance effects, e.g. near a hip prosthesis. Imaging of the pelvic vessels and suprarenal aorta was performed during free-breathing with satisfactory image quality in our cohort of subjects. Respiratory compensation might be necessary to avoid motion artifacts in some subjects. In very small vessels with rapid laminar flow, it may be difficult to accurately discern the leading edge of the labeled bolus. Furthermore, while cFASL is well-suited to measuring flow velocities over limited portions of the cardiac cycle, phase contrast techniques are easier to apply when flow measurements are required over the entire cardiac cycle. Finally, the finite temporal resolution of both cFASL and 2DPC may negatively impact the accuracy of peak velocity measurements.
This feasibility study suggests that cFASL provides an efficient, high quality and physiologically accurate display of in-plane flow patterns over extensive lengths of the abdominal aorta and lower extremity peripheral arteries. Further studies will be required to determine the value of this technique in patients with peripheral arterial disease.
Availability of data and materials
The datasets used and/or analyzed during the current study are available from the corresponding author on reasonable request
2-dimensional phase contrast
Balanced steady-state free precession
cine fast interrupted steady-state in combination with arterial spin labeling
Common iliac artery
Cardiovascular magnetic resonance
Computed tomography angiography
Digital subtraction angiography
Fast interrupted steady state
Maximal image projection
Magnetic resonance angiography
Peripheral arterial disease
Quiescent interval slice-selective
Superficial femoral artery
Vos T, Flaxman AD, Naghavi M, Lozano R, Michaud C, Ezzati M, et al. Years lived with disability (YLDs) for 1160 sequelae of 289 diseases and injuries 1990-2010: a systematic analysis for the global burden of disease study 2010. Lancet. 2012;380:2163–96.
Guthaner DF, Wexler L, Enzmann DR, Riederer SJ, Keyes GS, Collins WF, et al. Evaluation of peripheral vascular disease using digital subtraction angiography. Radiology. 1983;147:393–8.
Gerhard-Herman MD, Gornik HL, Barrett C, Barshes NR, Corriere MA, Drachman DE, et al. 2016 AHA/ACC guideline on the Management of Patients with Lower Extremity Peripheral Artery Disease: a report of the American College of Cardiology/American Heart Association task force on clinical practice guidelines. J Am Coll Cardiol. 2017;69(11):e71–e126.
Layden J, Michaels J, Bermingham S, Higgins B. Diagnosis and management of lower limb peripheral arterial disease: summary of NICE guidance. BMJ. 2012;345:e4947.
Norgren L, Hiatt WR, Dormandy JA, Nehler MR, Harris KA, Fowkes FGR. Inter-society consensus for the Management of Peripheral Arterial Disease (TASC II). Eur J Vasc Endovasc Surg. 2007;33(Suppl 1):S1–75.
Hennig J, Scheffler K, Laubenberger J, Strecker R. Time-resolved projection angiography after bolus injection of contrast agent. Magn Reson Med. 1997;3:341–5.
Korosec FR, Frayne R, Grist TM, Mistretta CA. Time-resolved contrast-enhanced 3D MR angiography. Magn Reson Med. 1996;36:345–51.
Edelman RR, Serhal A, Pursnani A, Pang J, Koktzglou I. Cardiovascular cine imaging and flow evaluation using fast interrupted steady-state (FISS) magnetic resonance. J Cardiovasc Magn Reson. 2018;20(1):12.
Edelman RR, Sheehan JJ, Dunkle E, Schindler N, Carr J, Koktzglou I. Quiescent-interval single-shot unenhanced magnetic resonance angiography of peripheral vascular disease: technical considerations and clinical feasibility. Magn Reson Med. 2010;63:951–8.
Bland JM, Altman DG. Statistical methods for assessing agreement between two methods of clinical measurement. Lancet. 1986;1:307–10.
Koktzoglou I, Edelman RR. Radial fast interrupted steady-state (FISS) magnetic resonance imaging. Magn Reson Med. 2018;79:2077–86.
Derbyshire JA, Herzka DA, McVeigh ER. S5FP: spectrally selective suppression with steady state free precession. Magn Reson Med. 2005;54(4):918–28.
Lee VS. Cardiovascular MR imaging: physical principles to practical protocols. 1st ed. Philadelphia: Lippincott Williams & Wilkins; 2005. p. 185.
Moran PR. A flow velocity zeugmatographic interlace for NMR imaging in humans. Magn Reson Imaging. 1982;1:197–203.
Bryant DJ, Payne JA, Firmin DN, Longmore DB. Measurement of flow with NMR imaging using a gradient pulse and phase difference technique. J Comput Assist Tomogr. 1984;8:588–93.
McCauley TR, Pena CS, Holland CK, Price TB, Gore JC. Validation of volume flow measurements with cine phase-contrast MR imaging for peripheral arterial waveforms. J Magn Reson Imaging. 1995;5:663–8.
Reimer P, Boos M. Phase-contrast MR angiography of peripheral arteries: technique and clinical application. Eur Radiol. 1999;9:122–7.
Steffens JC, Link J, Müller-Hülsbeck S, Freund M, Brinkmann G, Heller M. Cardiac-gated two-dimensional phase-contrast MR angiography of lower extremity occlusive disease. Am J Roentgenol. 1997;169:749–54.
Rose MJ, Jarvis K, Chowdhary V, Barker AJ, Allen BD, Robinson JD, et al. Efficient method for volumetric assessment of peak blood flow velocity using 4D flow MRI. J Magn Reson Imaging. 2016;44:1673–82.
Frydrychowicz A, Winterer JT, Zaitsev M, Jung B, Hennig J, Langer M, et al. Visualization of iliac and proximal femoral artery hemodynamics using time-resolved 3D phase contrast MRI at 3T. J Magn Reson Imaging. 2007;25(5):1085–92.
We wish to acknowledge Ms. Claire Feczko, our study coordinator and Dr. Wei Li and Nondas Leloudas for assisting with data collection and analysis.
NIH grants R01 HL137920 and R01 HL130093
Ethics approval and consent to participate
The study was approved by the Institutional Review Board of NorthShore University HealthSystem, Illinois (IORG0000308). The healthy volunteers and the patients with known peripheral artery disease in whom the lower extremities were evaluated provided written, informed consent in an IRB-approved study. For the patients in whom images were acquired through the suprarenal segment of the abdominal aorta during a clinically-indicated CMR exam, there was an IRB-approved waiver of consent.
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IK: Research support from Siemens Healthcare
RRE: Research support and royalty arrangement with Siemens Healthcare
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Aherne, E.A., Koktzoglou, I., Lind, B.B. et al. Dynamic quantitative nonenhanced magnetic resonance angiography of the abdominal aorta and lower extremities using cine fast interrupted steady-state in combination with arterial spin labeling: a feasibility study. J Cardiovasc Magn Reson 21, 55 (2019). https://doi.org/10.1186/s12968-019-0562-3
- Peripheral artery disease
- Magnetic resonance imaging
- Flow measurement
- Fast interrupted steady-state
- Quiescent interval slice-selective