GlucoCEST imaging with on‐resonance variable delay multiple pulse (onVDMP) MRI

Xu, Xiang; Xu, Jiadi; Chan, Kannie W. Y.; Liu, Jing; Huanling, L; Li, Yuguo; Chen, Lin; Liu, Guanshu; Zijl, Peter van

doi:10.1002/mrm.27364

Cited by 29 publications

(47 citation statements)

References 43 publications

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“…In order to improve DGE acquisitions, several approaches are possible, which will need to be tested in future work. Most logical would be to improve the effect size, an example of which was shown recently in animals at ultra high field using a pulsed CEST approach . Similar to other approaches, such as diffusion imaging, the methodology would benefit from fast 3D acquisition and the use of navigator echoes.…”

Section: Discussionmentioning

confidence: 99%

“…Most logical would be to improve the effect size, an example of which was shown recently in animals at ultra high field using a pulsed CEST approach. 40 Similar to other approaches, such as diffusion imaging, the methodology would benefit from fast 3D acquisition and the use of navigator echoes. A limitation of the current study is that possible dynamic changes in the B 0 field (e.g., frequency shifts because of susceptibility changes) cannot be separated out from the effects measured.…”

Section: Technical Considerationsmentioning

confidence: 99%

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d‐glucose weighted chemical exchange saturation transfer (glucoCEST)‐based dynamic glucose enhanced (DGE) MRI at 3T: early experience in healthy volunteers and brain tumor patients

Sehgal

Yadav

et al. 2019

Magnetic Resonance in Med

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Purpose Dynamic glucose enhanced (DGE) MRI has shown potential for imaging glucose delivery and blood–brain barrier permeability at fields of 7T and higher. Here, we evaluated issues involved with translating d‐glucose weighted chemical exchange saturation transfer (glucoCEST) experiments to the clinical field strength of 3T. Methods Exchange rates of the different hydroxyl proton pools and the field‐dependent T2 relaxivity of water in d‐glucose solution were used to simulate the water saturation spectra (Z‐spectra) and DGE signal differences as a function of static field strength B0, radiofrequency field strength B1, and saturation time tsat. Multislice DGE experiments were performed at 3T on 5 healthy volunteers and 3 glioma patients. Results Simulations showed that DGE signal decreases with B0, because of decreased contributions of glucoCEST and transverse relaxivity, as well as coalescence of the hydroxyl and water proton signals in the Z‐spectrum. At 3T, because of this coalescence and increased interference of direct water saturation and magnetization transfer contrast, the DGE effect can be assessed over a broad range of saturation frequencies. Multislice DGE experiments were performed in vivo using a B1 of 1.6 µT and a tsat of 1 second, leading to a small glucoCEST DGE effect at an offset frequency of 2 ppm from the water resonance. Motion correction was essential to detect DGE effects reliably. Conclusion Multislice glucoCEST‐based DGE experiments can be performed at 3T with sufficient temporal resolution. However, the effects are small and prone to motion influence. Therefore, motion correction should be used when performing DGE experiments at clinical field strengths.

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Section: Discussionmentioning

confidence: 99%

Section: Technical Considerationsmentioning

confidence: 99%

d‐glucose weighted chemical exchange saturation transfer (glucoCEST)‐based dynamic glucose enhanced (DGE) MRI at 3T: early experience in healthy volunteers and brain tumor patients

Sehgal

Yadav

et al. 2019

Magnetic Resonance in Med

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“…In vivo MRI scans were performed on an 11.7T horizontal bore Bruker scanner (Biospec, MA), with a 72mm quadrature transmitter coil and an eight-channel phased- array mouse body receiver coil. The onVDMP labeling module [44] consisted of a train of 8 binomial RF pulses, each binomial pair made of two block pulses of opposite phase with a width of 1.5 ms (3 ms for the pair) and a peak power of 15.6 μT, corresponding to a flip angle of 360 degrees for each block pulse. The pulse train was played out with the offset on the water resonance and a 10 ms mixing time between pulse pairs was applied to remove unwanted traverse magnetization.…”

Section: Methodsmentioning

confidence: 99%

“…S1true¯base was kept constant as a baseline reference, S1 was obtained every 10 sec time point, and S0 was updated every minute in the corresponding acquisition block to account for possible fluctuation in the water proton density after infusion. This definition of Δ S N follows our previous publications on DGE MRI [39, 42, 44]. Δ S N values acquired between 10–25 min after the start of the protocol (or 5–25 min post infusion) were summed as the area under the curve (AUC15min), as a surrogate marker for glucose uptake and transport in the placenta.…”

Section: Methodsmentioning

confidence: 99%

“…In contrast to CW- CEST that targets a single off-resonance frequency, the onVDMP method efficiently labels a range of fast-exchanging protons, covering multiple resonance frequencies of the five hydroxyl protons with exchange rates between 3–6kHz. It has been demonstrated that DGE signal changes in the brain detected by onVDMP were about two times higher than those measure by CW-CEST [44]. In this study, we investigated the feasibility of onVDMP-based DGE to monitor glucose kinetics in normal and injured placentae.…”

Section: Introductionmentioning

confidence: 99%

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Dynamic glucose enhanced MRI of the placenta in a mouse model of intrauterine inflammation

Lei

et al. 2018

Placenta

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Relayed nuclear Overhauser enhancement imaging with magnetization transfer contrast suppression at 3 T

Huang

Han

Chen

et al. 2020

Magnetic Resonance in Med

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Purpose: To develop a pulsed CEST magnetization-transfer method for rapidly acquiring relayed nuclear Overhauser enhancement (rNOE)-weighted images with magnetic transfer contrast (MTC) suppression at clinical field strength (3 T). Methods: Using a pulsed CEST magnetization-transfer method with low saturation powers (B 1) and long mixing time (t mix) to suppress contributions due to strong MTC from solid-like macromolecules, a low B 1 also minimized direct water saturation. These MTC contributions were further reduced by subtracting the Z-spectral signals at two or three offsets by assuming that the residual MTC is a linear function between −3.5 ppm and −12.5 ppm. Results: Phantom studies of a lactic acid (Lac) solution mixed with cross-linked bovine serum albumin show that strong MTC interference has a significant impact on the optimum B 1 for detecting rNOEs, due to lactate binding. The MTC could be effectively suppressed using a pulse train with a B 1 of 0.8 μT, a pulse duration (t p) of 40 ms, a t mix of 60 ms, and a pulse number (N) of 30, while rNOE signal was well maintained. As a proof of concept, we applied the method in mouse brain with injected hydrogel and a cell-hydrogel phantom. Results showed that rNOE-weighted images could provide good contrast between brain/cell and hydrogel. Conclusion: The developed pulsed CEST magnetization-transfer method can achieve MTC suppression while preserving most of the rNOE signal at 3 T, which indicates the potential for translation of this technique to clinical applications related to mobile proteins/lipids change.

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GlucoCEST imaging with on‐resonance variable delay multiple pulse (onVDMP) MRI

Abstract: The onVDMP method is a more sensitive technique for the detection of exogenous CEST agents with fast-exchanging protons compared to CW-CEST MRI.

Cited by 29 publications

References 43 publications

d‐glucose weighted chemical exchange saturation transfer (glucoCEST)‐based dynamic glucose enhanced (DGE) MRI at 3T: early experience in healthy volunteers and brain tumor patients

d‐glucose weighted chemical exchange saturation transfer (glucoCEST)‐based dynamic glucose enhanced (DGE) MRI at 3T: early experience in healthy volunteers and brain tumor patients

Dynamic glucose enhanced MRI of the placenta in a mouse model of intrauterine inflammation

Relayed nuclear Overhauser enhancement imaging with magnetization transfer contrast suppression at 3 T

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