[1-13C]urea and [1-13C]acetate phantoms (with a spectral separation of 1890 Hz at 9.4 T) were scanned to explore image properties of the accelerated acquisition using a 9.4 T horizontal bore magnet (Agilent, Yarnton, UK) with VnmrJ 4.0A (Agilent, Santa Clara, California). A dual-tuned 13C/1H volume rat coil (Doty Scientific, Columbia, South Carolina) was used for 1H and 13C magnetic resonance imaging. A standard slice-selective 2-dimensional 13C CSI sequence was used for imaging the phantoms. Parameters were as follows: flip angle = 10°, a Cartesian k-space trajectory, matrix = 32 × 32, repetition time/echo time = 200 ms/0.67 ms, field of view = 60 × 60 mm2, average = 4, spectral width =6000 Hz, number of points =[256 128 64 42 32 16] complex points, and an axial slice thickness of 20 mm. FPT reconstruction of the accelerated data was compared with the iterative decomposition of water and fat with echo asymmetry and least-squares estimation (IDEAL) method to assess the image quality (31 (link)).
9.4 t horizontal bore magnet
Manufactured by Agilent Technologies
Sourced in United Kingdom
The 9.4 T horizontal bore magnet is a high-field superconducting magnet designed for magnetic resonance applications. It features a horizontal bore configuration and a magnetic field strength of 9.4 Tesla. The magnet is constructed using superconducting materials to generate a stable and homogeneous magnetic field.
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5 protocols using 9.4 t horizontal bore magnet
1
Accelerated 13C Imaging using Phantoms
2
Accelerated 13C MRI Phantom Imaging
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[1-13C]urea and [1-13C]acetate phantoms (with a spectral separation of 1890 Hz at 9.4 T) were scanned to explore image properties of the accelerated acquisition using a 9.4 T horizontal bore magnet (Agilent, Yarnton, UK) with VnmrJ 4.0A (Agilent, Santa Clara, California). A dual-tuned 13C/1H volume rat coil (Doty Scientific, Columbia, South Carolina) was used for 1H and 13C magnetic resonance imaging. A standard slice-selective 2-dimensional 13C CSI sequence was used for imaging the phantoms. Parameters were as follows: flip angle = 10°, a Cartesian k-space trajectory, matrix = 32 × 32, repetition time/echo time = 200 ms/0.67 ms, field of view = 60 × 60 mm2, average = 4, spectral width = 6000 Hz, number of points = [256 128 64 42 32 16] complex points, and an axial slice thickness of 20 mm. FPT reconstruction of the accelerated data was compared with the iterative decomposition of water and fat with echo asymmetry and least-squares estimation (IDEAL) method to assess the image quality (31 (link)).
3
Quantifying Visceral Fat Volumes
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Animals were anesthetized using isoflurane (4% for sleep induction and ~2% for sleep maintenance) in a 3:7 mixture of oxygen and air, before being positioned prone in the MR-compatible animal holder. Respiration was monitored during scanning (SA-instruments, Stony Brook, NY, USA). Core body temperature was maintained at 37 °C during scanning using a warm air system (SA-Instruments, Stony Brook, NY, USA). Magnetic resonance imaging images (n = 5–7 per group) were collected using a 9.4 T horizontal bore magnet (Varian, Yarnton, UK) equipped with a 40 mm millipede coil, as detailed5 (link). Fiji software (http://fiji.sc ) was used to compute the volume of fat in different regions of interest in the body. Visceral fat was calculated as the difference between the total fat and the subcutaneous fat signal in the abdominal region. Total subcutaneous fat was calculated as the differences between total fat and visceral fat. Experiment was performed on the same mouse (F1) at the age of 3 months (MID) and 6 months (END).
4
In Vivo Magnetic Resonance Spectroscopy of Visceral and Subcutaneous Fat
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The magnetic resonance imaging experiments were conducted on the same mouse at week 14 and week 25 using a 9.4 T horizontal bore magnet (Varian Yarnton UK) equipped with a 40 mm millipede coil, as previously described [49 (link)]. Localized 1H-MRS from visceral and subcutaneous fat depots were acquired from 2 × 1.5 × 1.5 mm3 voxels positioned in the upper gonadal abdominal fat (as representative of visceral fat) and in the inguinal abdominal fat (as representative of the subcutaneous fat) (Fig. 2a ).
5
Quantifying Body Fat in Mice via MRI
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Animals were anesthetized using isoflurane (4% for sleep induction and ~2% for sleep maintenance) in a 3:7 mixture of oxygen and air, before being positioned prone in the MR-compatible animal holder. Respiration was monitored during scanning (SA-instruments, Stony Brook, NY, USA). Core body temperature was maintained at 37 °C during scanning using a warm air system (SA-instruments, Stony Brook, NY, USA).
The MRI experiments (n = 6–7 per group) were conducted using a 9.4 T horizontal bore magnet (Varian, Yarnton, UK) equipped with a 40-mm millipede coil, as previously detailed45 (link). All images were collected on the matrix size 256 × 96 and a field-of-view of 51.2 × 51.2 mm2. Fiji software (http://fiji.sc ) was used to compute the volume of total fat (TF), visceral fat (VAT), and total subcutaneous fat (SAT). VAT was calculated as the difference between the TF signal and SAT signal in the abdominal region. MRI experiments were performed on the same mouse (F1) at P80 (MID) and P150 (END).
The MRI experiments (n = 6–7 per group) were conducted using a 9.4 T horizontal bore magnet (Varian, Yarnton, UK) equipped with a 40-mm millipede coil, as previously detailed45 (link). All images were collected on the matrix size 256 × 96 and a field-of-view of 51.2 × 51.2 mm2. Fiji software (
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