In Vivo Cerebral 31P Magnetic Resonance Spectroscopy

Cady, Ernest B.

doi:10.1007/978-1-4614-1788-0_6

Cited by 5 publications

(6 citation statements)

References 129 publications

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“…The detection of 31 P nuclei by magnetic resonance (MR), however, suffers from lower sensitivity than 1 H nuclei because of its lower magnetogyric ratio . Consequently, high quality 31 P NMR spectra or MR images require relatively large amounts of sample in conjunction with signal averaging.…”

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confidence: 99%

“…13,14 The detection of 31 P nuclei by magnetic resonance (MR), however, suffers from lower sensitivity than 1 H nuclei because of its lower magnetogyric ratio. 15 Consequently, high quality 31 P NMR spectra or MR images require relatively large amounts of sample in conjunction with signal averaging. Hyperpolarization techniques are seen as a route to overcome this low sensitivity issue which arises from the small population difference (ca.…”

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confidence: 99%

“…In this case, the p-H 2 refresh step involves the short-lived iridium dihydrogen dihydride complex 3. To date, reported studies using the SABRE approach have focused on the polarization of 1 H 29,32−34 and 13 C 29,35 nuclei, although 15 N 36,37 19 F 29 and 31 P 28,38 signals have been seen when polarized. Both of the 31 P studies focused on PPh 3 , with Koptyug et al reporting that the signal for free PPh 3 can be enhanced by 2 orders of magnitude, and a single shot image recorded at 9.4 T. 38 Importantly, SABRE has been shown to be successful for a growing range of biologically relevant molecules; this has established the potential of the method to produce 1 H and 13 C hyperpolarized agents for subsequent MRI measurement.…”

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confidence: 99%

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Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design

et al. 2015

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Traditional 31P NMR or MRI measurements suffer from low sensitivity relative to 1H detection and consequently require longer scan times. We show here that hyperpolarization of 31P nuclei through reversible interactions with parahydrogen can deliver substantial signal enhancements in a range of regioisomeric phosphonate esters containing a heteroaromatic motif which were synthesized in order to identify the optimum molecular scaffold for polarization transfer. A 3588-fold 31P signal enhancement (2.34% polarization) was returned for a partially deuterated pyridyl substituted phosphonate ester. This hyperpolarization level is sufficient to allow single scan 31P MR images of a phantom to be recorded at a 9.4 T observation field in seconds that have signal-to-noise ratios of up to 94.4 when the analyte concentration is 10 mM. In contrast, a 12 h 2048 scan measurement under standard conditions yields a signal-to-noise ratio of just 11.4. 31P-hyperpolarized images are also reported from a 7 T preclinical scanner.

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Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design

et al. 2015

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“…MRS can not only provide information on biochemical changes in response to tumor growth but also delineate different metabolic tumor phenotypes. For instance, 1 H MRS is widely used to monitor metabolic changes in cancer tissue [ 41 – 47 ], and the other active nuclei such as 31 P (phosphorus) [ 48 , 49 ], 23 Na (sodium) [ 50 ], 13 C (carbon) [ 51 – 53 ], and 19 F (fluorine) [ 54 , 55 ] are also being used to monitor bioenergetics and metabolic in cancer.…”

Section: Molecular Imaging Modelsmentioning

confidence: 99%

Multimodal Molecular Imaging: Current Status and Future Directions

Shu

2018

Contrast Media & Molecular Imaging

104

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Molecular imaging has emerged at the end of the last century as an interdisciplinary method involving in vivo imaging and molecular biology aiming at identifying living biological processes at a cellular and molecular level in a noninvasive manner. It has a profound role in determining disease changes and facilitating drug research and development, thus creating new medical modalities to monitor human health. At present, a variety of different molecular imaging techniques have their advantages, disadvantages, and limitations. In order to overcome these shortcomings, researchers combine two or more detection techniques to create a new imaging mode, such as multimodal molecular imaging, to obtain a better result and more information regarding monitoring, diagnosis, and treatment. In this review, we first describe the classic molecular imaging technology and its key advantages, and then, we offer some of the latest multimodal molecular imaging modes. Finally, we summarize the great challenges, the future development, and the great potential in this field.

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“…Here, we adopt for GPC and α-NTP, values of 2.97 ppm and −7.57 ppm, respectively, as measured in mammalian brain. 40 For the FID spectrum, we use the α-NTP resonance as it is most clear, whereas the GPC signal in FID is affected by mobile phospholipid; for the echo spectra, we take GPC as chemical shift reference. In this way, we have six measurements (one FID and five echoes) for the chemical shift of Pi which is, on average, 5.31 ± 0.05 ppm, corresponding to a pH value of 7.51 ± 0.07.…”

Section: Reproducibilitymentioning

confidence: 99%

Proton and phosphorus magnetic resonance spectroscopy of the healthy human breast at 7 T

et al. 2016

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In vivo water‐ and fat‐suppressed 1H magnetic resonance spectroscopy (MRS) and 31P magnetic resonance adiabatic multi‐echo spectroscopic imaging were performed at 7 T in duplicate in healthy fibroglandular breast tissue of a group of eight volunteers. The transverse relaxation times of 31P metabolites were determined, and the reproducibility of 1H and 31P MRS was investigated. The transverse relaxation times for phosphoethanolamine (PE) and phosphocholine (PC) were fitted bi‐exponentially, with an added short T 2 component of 20 ms for adenosine monophosphate, resulting in values of 199 ± 8 and 239 ± 14 ms, respectively. The transverse relaxation time for glycerophosphocholine (GPC) was also fitted bi‐exponentially, with an added short T 2 component of 20 ms for glycerophosphatidylethanolamine, which resonates at a similar frequency, resulting in a value of 177 ± 6 ms. Transverse relaxation times for inorganic phosphate, γ‐ATP and glycerophosphatidylcholine mobile phospholipid were fitted mono‐exponentially, resulting in values of 180 ± 4, 19 ± 3 and 20 ± 4 ms, respectively. Coefficients of variation for the duplicate determinations of 1H total choline (tChol) and the 31P metabolites were calculated for the group of volunteers. The reproducibility of inorganic phosphate, the sum of phosphomonoesters and the sum of phosphodiesters with 31P MRS imaging was superior to the reproducibility of 1H MRS for tChol. 1H and 31P data were combined to calculate estimates of the absolute concentrations of PC, GPC and PE in healthy fibroglandular tissue, resulting in upper limits of 0.1, 0.1 and 0.2 mmol/kg of tissue, respectively.

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In Vivo Cerebral 31P Magnetic Resonance Spectroscopy

Cited by 5 publications

References 129 publications

Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design

Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design

Multimodal Molecular Imaging: Current Status and Future Directions

Proton and phosphorus magnetic resonance spectroscopy of the healthy human breast at 7 T

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In Vivo Cerebral 31P Magnetic Resonance Spectroscopy

Cited by 5 publications

References 129 publications

Improving the Hyperpolarization of 31P Nuclei by Synthetic Design

Improving the Hyperpolarization of 31P Nuclei by Synthetic Design

Multimodal Molecular Imaging: Current Status and Future Directions

Proton and phosphorus magnetic resonance spectroscopy of the healthy human breast at 7 T

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Product

Resources

About

Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design

Improving the Hyperpolarization of ³¹P Nuclei by Synthetic Design