Perfusion Imaging with Echo-Planar Imaging

Stehling, Michael K.; Brüning, R.; Rosen, Bruce R.

doi:10.1007/978-3-642-80443-4_13

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Section 3: Bolus Tracking Techniques1

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2005

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Cited by 4 publications

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“…can be used. Because of its signal‐to‐noise ratio (SNR) advantage and of its time resolution, EPI is the reference method to monitor bolus injection (67). Due to its intrinsically low sensitivity to motion artifacts, spiral imaging could also be advantageous.…”

Section: Section 3: Bolus Tracking Techniquesmentioning

confidence: 99%

Methodology of brain perfusion imaging

Barbier

Lamalle

Décorps

2001

Magnetic Resonance Imaging

376

288

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Section: Section 3: Bolus Tracking Techniquesmentioning

confidence: 99%

Methodology of brain perfusion imaging

Barbier

Lamalle

Décorps

2001

Magnetic Resonance Imaging

376

288

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Arterial input functions for dynamic susceptibility contrast MRI: Requirements and signal options

Conturo

Akbudak

Kotys

et al. 2005

Magnetic Resonance Imaging

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Cerebral perfusion imaging using dynamic susceptibility contrast (DSC) has been the subject of considerable research and shows promise for basic science and clinical use. In DSC, the MRI signals in brain tissue and feeding arteries are monitored dynamically in response to a bolus injection of paramagnetic agents, such as gadolinium (Gd) chelates. DSC has the potential to allow quantitative imaging of parameters such as cerebral blood flow (CBF) with a high signal‐to‐noise ratio (SNR) in a short scan time; however, quantitation depends critically on accurate and precise measurement of the arterial input function (AIF). We discuss many requirements and factors that make it difficult to measure the AIF. The AIF signal should be linear with respect to Gd concentration, convertible to the same concentration scale as the tissue signal, and independent of hematocrit. Complicated relationships between signal and concentration can violate these requirements. The additional requirements of a high SNR and high spatial/temporal resolution are technically challenging. AIF measurements can also be affected by signal saturation and aliasing, as well as dispersion/delay between the AIF sampling site and the tissue. We present new in vivo preliminary results for magnitude‐based (ΔR2*) and phase‐based (Δϕ) AIF measurements that show a linearity advantage of phase, and a disparity in the scaling of Δϕ AIFs, ΔR2* AIFs, and ΔR2* tissue curves. Finally, we discuss issues related to the choice of AIF signal for quantitative perfusion imaging. J. Magn. Reson. Imaging 2005. © 2005 Wiley‐Liss, Inc.

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