Implementation of a rapid inversion-prepared dual-contrast gradient echo sequence for quantitative dynamic contrast-enhanced magnetic resonance imaging of the human prostate

Prochnow, Daniel; Beyersdorff, Dirk; Warmuth, Carsten; Taupitz, Matthias; Gemeinhardt, Ole; Lüdemann, Lutz

doi:10.1016/j.mri.2005.09.010

Cited by 14 publications

(32 citation statements)

References 26 publications

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“…If the SR prepulse is replaced with an inversion recovery (IR) prepulse, all of the longitudinal magnetization is available for measuring SI, which is why an IR pulse sequence is more sensitive to changes in relaxivity; however, the image acquisition time is also longer. Once again, a linear relationship can be expected between SI and [CM] for the low [CM] range of ≤4 mmol/l; the concentration is likely to be within this range, unless images are acquired in the early distribution phase [25]. However, if the MR sequence also serves to adequately quantify the early distribution phase, especially the first pass of the CM, then one must consider the T2* effects as well; these effects are proportional to [CM] and reduce the T1 signal [25,26].…”

Section: Dce-mrimentioning

confidence: 99%

“…Once again, a linear relationship can be expected between SI and [CM] for the low [CM] range of ≤4 mmol/l; the concentration is likely to be within this range, unless images are acquired in the early distribution phase [25]. However, if the MR sequence also serves to adequately quantify the early distribution phase, especially the first pass of the CM, then one must consider the T2* effects as well; these effects are proportional to [CM] and reduce the T1 signal [25,26]. To capture these effects, a dual-echo GRE sequence is used, which acquires T1w and T2*w images simultaneously [25][26][27].…”

Section: Dce-mrimentioning

confidence: 99%

“…However, if the MR sequence also serves to adequately quantify the early distribution phase, especially the first pass of the CM, then one must consider the T2* effects as well; these effects are proportional to [CM] and reduce the T1 signal [25,26]. To capture these effects, a dual-echo GRE sequence is used, which acquires T1w and T2*w images simultaneously [25][26][27]. The dual-echo sequence thus allows sensitive measurement of the SI of low tissue [CM] along with the sensitive measurement of the SI of high [CM] for extracting the individual AIF.…”

Section: Dce-mrimentioning

confidence: 99%

“…The measured MR SI are converted into [CM] by fitting an analytical concentrationtime curve to the SI-time curves measured in the central artery, which is subject to the dependencies already described in the DCE-MRI section above. As a result of the highly concentrated CM bolus, especially during first pass, the measured T1w SI must be corrected for the signallowering T2* effect [25,26]. Temporal resolution should not exceed 2 s in order to ensure adequate tracking of the arrival and passage of the contrast medium bolus [33].…”

Section: Arterial Input Functionmentioning

confidence: 99%

“…Therefore, an open sequential 3-compartment model has been proposed and used for the prostate and prostate cancer. This model comprises blood plasma as one compartment and two EES compartments [25,47]. Using this model, quantification of blood flow in a tissue voxel is based on the so-called indicator dilution method and the calculated AIF [48].…”

Section: Pharmacokinetic Modelsmentioning

confidence: 99%

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Dynamic contrast-enhanced magnetic resonance imaging and pharmacokinetic models in prostate cancer

2010

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Dynamic contrast-enhanced MRI enables noninvasive analysis of prostate vascularization as well as tumour angiogenesis and capillary permeability characteristics in prostate cancers. Pharmacokinetic models summarizing the complex information provided by signal intensity-time curves for a few quantitative pharmacokinetic parameters are increasingly being used in the routine clinical setting. This review consists of two parts. The first part discusses the advantages and disadvantages of the MR pulse sequences that can be used for performing DCE-MRI and also of the most widely used pharmacokinetic parameters and models and the parameters they describe. The second part outlines the range of current and potential future clinical applications of DCE-MRI and pharmacokinetic parametric maps in patients with prostate cancer, with reference to the current scientific literature on the topic. The potential clinical applications of DCE-MRI for prostate cancer include detection, localization, and staging, differentiation of recurrent cancer and estimation of the patient's prognosis, as well as monitoring of treatment response.

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Section: Dce-mrimentioning

confidence: 99%

Section: Dce-mrimentioning

confidence: 99%

Section: Dce-mrimentioning

confidence: 99%

Section: Arterial Input Functionmentioning

confidence: 99%

Section: Pharmacokinetic Modelsmentioning

confidence: 99%

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Dynamic contrast-enhanced magnetic resonance imaging and pharmacokinetic models in prostate cancer

2010

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Assessment of the effect of haematocrit‐dependent arterial input functions on the accuracy of pharmacokinetic parameters in dynamic contrast‐enhanced MRI

et al. 2011

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The detection and prognosis of prostate cancer in its early stages are critically important. It is therefore essential to improve the existing dynamic contrast-enhanced MRI (DCE MRI) techniques commonly used for the assessment of the tumour vascular environment. The goal of this study was to describe a method for the estimation of the arterial input function (AIF) in DCE MRI by measuring R(2) * values in the femoral artery of patients with early-stage prostate cancer. The calculation of contrast agent concentrations was based on calibration curves determined in whole blood samples for a range of normal haematocrit (HCT) values (HCT = 0.35-0.525). Individual AIFs corrected for HCT were compared with individual AIFs calibrated with a mean whole blood [R(2)*-Gd-DTPA-BMA] [Gd-DTPA-BMA, gadolinium diethylenetriaminepentaacetate-bis(methylamide) (gadodiamide)] curve at an assumed HCT = 0.44, as well as a population AIF at an assumed HCT = 0.45. The area under the curve of the first-pass bolus ranged between 0.6 min mM at HCT = 0.53 and 1.3 min mM at HCT = 0.39. Significant differences in magnitude at peak contrast agent concentrations (HCT = 0.36, [Gd-DTPA-BMA](max) = 9 ± 0.4 mM; HCT = 0.46, [Gd-DTPA-BMA](max) = 4.0 ± 0.2 mM) were found. Using model-based simulations, the accuracy of the kinetic parameters estimated using individual AIFs corrected for HCT demonstrated that, for the use of individual calibration curves with HCT values differing by more than 10%, K(trans) and k(ep) values were largely underestimated (up to 60% difference for K(trans)). Moreover, blood volume estimates were severely underestimated. Estimates of kinetic parameters in early-stage prostate cancer patients demonstrated that the efflux rate constant (k(ep)) was influenced significantly by the definition of AIF. Regardless of whether an individually calibrated AIF or a population AIF (average of all individually calibrated AIFs) was used, pixel-by-pixel mapping of k(ep) and v(b) in the prostate gland appeared to be more sensitive than with the usual biexponential approach.

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Pelvis

Sala¹,

Hricak²,

Mueller-Lisse³

et al.

Magnetic Resonance Tomography

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Implementation of a rapid inversion-prepared dual-contrast gradient echo sequence for quantitative dynamic contrast-enhanced magnetic resonance imaging of the human prostate

Cited by 14 publications

References 26 publications

Dynamic contrast-enhanced magnetic resonance imaging and pharmacokinetic models in prostate cancer

Dynamic contrast-enhanced magnetic resonance imaging and pharmacokinetic models in prostate cancer

Assessment of the effect of haematocrit‐dependent arterial input functions on the accuracy of pharmacokinetic parameters in dynamic contrast‐enhanced MRI

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