Abstract

Liver dynamic contrast enhanced (DCE) MRI pharmacokinetic modelling could be useful in the assessment of diffuse liver disease and focal liver lesions, but is compromised by errors in arterial input function (AIF) sampling. In this study, we apply cardiac output correction to arterial input functions (AIFs) for liver DCE MRI and investigate the effect on dual-input single compartment hepatic perfusion parameter estimation and reproducibility.Thirteen healthy volunteers (28.7 ± 1.94 years, seven males) underwent liver DCE MRI and cardiac output measurement using aortic root phase contrast MRI (PCMRI), with reproducibility (n = 9) measured at 7 d. Cardiac output AIF correction was undertaken by constraining the first pass AIF enhancement curve using the indicator-dilution principle. Hepatic perfusion parameters with and without cardiac output AIF correction were compared and 7 d reproducibility assessed.Differences between cardiac output corrected and uncorrected liver DCE MRI portal venous (PV) perfusion (p = 0.066), total liver blood flow (TLBF) (p = 0.101), hepatic arterial (HA) fraction (p = 0.895), mean transit time (MTT) (p = 0.646), distribution volume (DV) (p = 0.890) were not significantly different. Seven day corrected HA fraction reproducibility was improved (mean difference 0.3%, Bland–Altman 95% limits-of-agreement (BA95%LoA) ±27.9%, coefficient of variation (CoV) 61.4% versus 9.3%, ±35.5%, 81.7% respectively without correction). Seven day uncorrected PV perfusion was also improved (mean difference 9.3 ml min−1/100 g, BA95%LoA ±506.1 ml min−1/100 g, CoV 64.1% versus 0.9 ml min−1/100 g, ±562.8 ml min−1/100 g, 65.1% respectively with correction) as was uncorrected TLBF (mean difference 43.8 ml min−1/100 g, BA95%LoA ±586.7 ml min−1/ 100 g, CoV 58.3% versus 13.3 ml min−1/100 g, ±661.5 ml min−1/100 g, 60.9% respectively with correction). Reproducibility of uncorrected MTT was similar (uncorrected mean difference 2.4 s, BA95%LoA ±26.7 s, CoV 60.8% uncorrected versus 3.7 s, ±27.8 s, 62.0% respectively with correction), as was and DV (uncorrected mean difference 14.1%, BA95%LoA ±48.2%, CoV 24.7% versus 10.3%, ±46.0%, 23.9% respectively with correction).Cardiac output AIF correction does not significantly affect the estimation of hepatic perfusion parameters but demonstrates improvements in normal volunteer 7 d HA fraction reproducibility, but deterioration in PV perfusion and TLBF reproducibility. Improved HA fraction reproducibility maybe important as arterialisation of liver perfusion is increased in chronic liver disease and within malignant liver lesions.

Highlights

  • Liver dynamic contrast enhanced (DCE) MRI has been used to investigate diffuse parenchymal changes in fibrosis/cirrhosis (Annet et al 2003, Hagiwara et al 2008, Kim et al 2008), and in the characterisation of focal liver lesion vascularity and quantification of tumour angiogenesis (Jackson et al 2002)

  • Perfusion parameters and residual sum of squares for model fitting across the sample are presented for uncorrected and corrected arterial input function (AIF) in figure 4 and table 2

  • Measurement of the AIF using MRI is troublesome and in this study we evaluate a previously proposed method in which independent measurements of cardiac output are used to correct AIFs (Zhang et al 2009)

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Summary

Introduction

Liver dynamic contrast enhanced (DCE) MRI has been used to investigate diffuse parenchymal changes in fibrosis/cirrhosis (Annet et al 2003, Hagiwara et al 2008, Kim et al 2008), and in the characterisation of focal liver lesion vascularity and quantification of tumour angiogenesis (Jackson et al 2002). Dynamic changes in tissue signal intensity (SI) are recorded, converted into CA concentration, with quantification of tissue perfusion using pharmacokinetic modelling (Tofts and Kermode 1991, Materne et al 2002, Pandharipande et al 2005). Pharmacokinetic modelling requires regions-of-interest (ROIs) to be placed over dynamically imaged afferent vessels to derive vascular input function (VIFs). These are measured following a rate-controlled injection, ideally directly into the afferent vessel and as close as possible to the organ of interest. VIFs are convolved with tissue enhancement curves to derive inflow and outflow constants that reflect perfusion

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