Multislice perfusion of the kidneys using parallel imaging: Image acquisition and analysis strategies

Gardener, Alexander G.; Francis, Susan T.

doi:10.1002/mrm.22387

Cited by 63 publications

(135 citation statements)

References 26 publications

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“…The timing of background suppression pulses is adjusted such that by the time of readout excitation, the static tissues of a predetermined range of T1 will be close to zero, while the fl ow contrast between tag and control images is preserved. We currently do not include background suppression in these values were comparable with those in previous studies ( 10,11,25,26 ). However, we found that measurements obtained with ASL and DCE MR imaging lacked correlation ( r = 0.32, P = .25) and consistency (ICC = 0.03) in the medulla.…”

Section: Genitourinary Imaging: Renal Perfusion 3-t Mr Imagingsupporting

confidence: 86%

“…In this regard, researchers ( 10 ) have suggested inclusion of respiratory gating to reduce motion-related degradation in image quality, data corruption, or both. While prospective gating prolongs examination time even in collaborative subjects and may become impractical in patients, retrospective gating entails extended measurement to collect enough images in the same phase of respiration.…”

Section: Genitourinary Imaging: Renal Perfusion 3-t Mr Imagingmentioning

confidence: 99%

See 1 more Smart Citation

Renal Perfusion 3-T MR Imaging: A Comparative Study of Arterial Spin Labeling and Dynamic Contrast-enhanced Techniques

Su²,

Chang³

et al. 2011

Radiology

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Purpose:To investigate the feasibility of and correlation between arterial spin-labeling (ASL) and dynamic contrast materialenhanced (DCE) 3-T magnetic resonance (MR) imaging in the measurement of renal blood fl ow (RBF). Materials and Methods:The review board approved this study. Nineteen healthy volunteers (seven women, 12 men; age range, 25-68 years) were recruited, and each provided written informed consent. MR imaging was performed with a 3-T whole-body system. Each subject underwent back-to-back ASL and DCE MR imaging. Ten runs of ASL imaging were performed by using the pseudocontinuous tagging scheme, and each run required an 18-second breath hold. For DCE imaging, a gadopentetate dimeglumine bolus (0.0125 mmol per kilogram of body weight) was administrated intravenously in all subjects except two; in the latter subjects, a 0.025 mmol/kg gadopentetate dimeglumine bolus was administered to evaluate the T1 saturation effect. RBF was quantifi ed with both techniques and in both the cortex and the medulla. Agreement was evaluated for RBF measurements obtained with ASL imaging and those obtained with DCE imaging by using correlation analysis. Results:RBF was apparently overestimated with 0.025 mmol/kg gadopentetate dimeglumine, which is a concentration that is commonly adopted for 1.5-T DCE. RBF was 227 mL/ 100 mL/min 6 30 (standard deviation) in the cortex and 101 mL/100 mL/min 6 21 in the medulla, as measured with ASL imaging, and 272 mL/100 mL/min 6 60 in the cortex and 122 mL/100 mL/min 6 30 in the medulla, as measured with DCE imaging. In the cortex, measurements obtained with ASL and DCE imaging exhibited a linear correlation ( r = 0.66; statistical power, 0.8 at the 5% signifi cance level) and fair agreement (intraclass correlation coeffi cient, 0.41). Conclusion:ASL and DCE 3-T MR imaging are feasible in the quantifi cation of cortical renal perfusion, yielding measurements that are correlated but not entirely comparable. Intermodality differences have yet to be solved.q RSNA, 2011

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Section: Genitourinary Imaging: Renal Perfusion 3-t Mr Imagingsupporting

confidence: 86%

Section: Genitourinary Imaging: Renal Perfusion 3-t Mr Imagingmentioning

confidence: 99%

Renal Perfusion 3-T MR Imaging: A Comparative Study of Arterial Spin Labeling and Dynamic Contrast-enhanced Techniques

Su²,

Chang³

et al. 2011

Radiology

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“…For example, different strategies have been employed to circumvent the problem of renal respiratory motion, including breath-holding, respiratory gating, or post processing registration. Gardener and Francis [19] found no difference in perfusion measurements made with either breath-holding or free breathing, but found reduced perfusion when background suppression was used to improve image quality, showing that some variations in imaging approach cause differences in perfusion measurements. Our ASL technique resulted in a scan time of 15 min, and breath-holding time of 12 s, which was tolerated by all participants.…”

Section: Discussionmentioning

confidence: 99%

Non-Contrast Renal Magnetic Resonance Imaging to Assess Perfusion and Corticomedullary Differentiation in Health and Chronic Kidney Disease

Gillis

McComb

Patel

et al. 2016

Nephron

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Aims: Arterial spin labelling (ASL) MRI measures perfusion without administration of contrast agent. While ASL has been validated in animals and healthy volunteers (HVs), application to chronic kidney disease (CKD) has been limited. We investigated the utility of ASL MRI in patients with CKD. Methods: We studied renal perfusion in 24 HVs and 17 patients with CKD (age 22-77 years, 40% male) using ASL MRI at 3.0T. Kidney function was determined using estimated glomerular filtration rate (eGFR). T1 relaxation time was measured using modified look-locker inversion and ﬂow-sensitive alternating inversion recovery true-fast imaging and steady precession was performed to measure cortical and whole kidney perfusion. Results: T1 was higher in CKD within cortex and whole kidney, and there was association between T1 time and eGFR. No association was seen between kidney size and volume and either T1, or ASL perfusion. Perfusion was lower in CKD in cortex (136 ± 37 vs. 279 ± 69 ml/min/100 g; p < 0.001) and whole kidney (146 ± 24 vs. 221 ± 38 ml/min/100 g; p < 0.001). There was significant, negative, association between T1 longitudinal relaxation time and ASL perfusion in both the cortex (r = -0.75, p < 0.001) and whole kidney (r = -0.50, p < 0.001). There was correlation between eGFR and both cortical (r = 0.73, p < 0.01) and whole kidney (r = 0.69, p < 0.01) perfusion. Conclusions: Significant differences in renal structure and function were demonstrated using ASL MRI. T1 may be representative of structural changes associated with CKD; however, further investigation is required into the pathological correlates of reduced ASL perfusion and increased T1 time in CKD.

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“…Singleslice ASL data acquisition, with a single slice acquired in a few hundred milliseconds, could significantly lead to label decay over the time course required to acquire a multislice data set. Alternatively, multislice kidney ASL data can be collected by repeating the single-slice acquisition procedure multiple times (8). Because ASL-fMRI remains challenging in RBF studies (2), animal models with invasive measurements of blood flow may be necessary for validation of this technique.…”

Section: Discussionmentioning

confidence: 99%

Arterial spin labeling blood flow magnetic resonance imaging for evaluation of renal injury

Liu

Song

Liang

et al. 2012

American Journal of Physiology-Renal Physiology

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Liu YP, Song R, Liang Ch, Chen X, Liu B. Arterial spin labeling blood flow magnetic resonance imaging for evaluation of renal injury. Am J Physiol Renal Physiol 303: F551-F558, 2012. First published May 30, 2012 doi:10.1152/ajprenal.00288.2011.-A multitude of evidence suggests that iodinated contrast material causes nephrotoxicity; however, there have been no previous studies that use arterial spin labeling (ASL) blood flow functional magnetic resonance imaging (fMRI) to investigate the alterations in effective renal plasma flow between normointensive and hypertensive rats following injection of contrast media. We hypothesized that FAIR-SSFSE arterial spin labeling MRI may enable noninvasive and quantitative assessment of regional renal blood flow abnormalities and correlate with disease severity as assessed by histological methods. Renal blood flow (RBF) values of the cortex and medulla of rat kidneys were obtained from ASL images postprocessed at ADW4.3 workstation 0.3, 24, 48, and 72 h before and after injection of iodinated contrast media (6 ml/kg). The H&E method for morphometric measurements was used to confirm the MRI findings. The RBF values of the outer medulla were lower than those of the cortex and the inner medulla as reported previously. Iodinated contrast media treatment resulted in decreases in RBF in the outer medulla and cortex in spontaneously hypertensive rats (SHR), but only in the outer medulla in normotensive rats. The iodinated contrast agent significantly decreased the RBF value in the outer medulla and the cortex in SHR compared with normotensive rats after injection of the iodinated contrast media. Histological observations of kidney morphology were also consistent with ASL perfusion changes. These results demonstrate that the RBF value can reflect changes of renal perfusion in the cortex and medulla. ASL-MRI is a feasible and accurate method for evaluating nephrotoxic drugs-induced kidney damage.

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Multislice perfusion of the kidneys using parallel imaging: Image acquisition and analysis strategies

Cited by 63 publications

References 26 publications

Renal Perfusion 3-T MR Imaging: A Comparative Study of Arterial Spin Labeling and Dynamic Contrast-enhanced Techniques

Renal Perfusion 3-T MR Imaging: A Comparative Study of Arterial Spin Labeling and Dynamic Contrast-enhanced Techniques

Non-Contrast Renal Magnetic Resonance Imaging to Assess Perfusion and Corticomedullary Differentiation in Health and Chronic Kidney Disease

Arterial spin labeling blood flow magnetic resonance imaging for evaluation of renal injury

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