9.4 t magnet

Manufactured by Agilent Technologies

Sourced in United States

The 9.4-T magnet is a high-field superconducting magnet designed for use in various laboratory and research applications. It provides a powerful magnetic field of 9.4 Tesla, which is suitable for advanced spectroscopy techniques and other research requiring strong magnetic fields.

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Lab products found in correlation

4.7 t magnet, by Agilent Technologies (1 mentions) Primovist, by Bayer (1 mentions) Avance 3 electronics, by Bruker (1 mentions) Dotarem, by Guerbet (1 mentions)

Close spelling variants of this product

Wide-bore (89 mm) 9.4 T vertical-bore magnet 9.4 T horizontal bore magnet

7 protocols using 9.4 t magnet

Ex Vivo Primate Brain Imaging

Cited 2 times

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MRI experiments, histological methods, and data registration were performed on an ex vivo squirrel monkey brain following the procedures described in [18 (link), 19 (link)]. Briefly, ex vivo imaging was performed a Varian 9.4 T magnet, with diffusion weighted scans acquired using a PGSE multi-shot spin-warp imaging sequence (TR = 4.6 s, TE = 42 ms, 32 gradient directions, b ≈ 1000s/mm², 300 μm voxel, 192×128×115 matrix). Diffusion processing was performed in “histology” space after registration (see below) using constrained spherical deconvolution [20 (link)] for voxel-wise reconstruction, resulting in diffusion FODs reconstructed in histology space.

Nath V., Schilling K.G., Remedios S., Bayrak R.G., Gao Y., Blaber J.A., Huo Y., Landman B.A, & Anderson A.W. (2019). LEARNING 3D WHITE MATTER MICROSTRUCTURE FROM 2D HISTOLOGY. Proceedings. IEEE International Symposium on Biomedical Imaging, 2019, 186-190.

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CW-CEST Imaging and Quantification

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A continuous wave (CW)-CEST sequence with a 5-second hard saturation pulse followed by single-shot spin-echo echo planar imaging (SE-EPI) acquisitions with a TR of 7 second was used on animal imaging. Images were acquired with matrix size 64 × 64, field of view 30 mm × 30 mm, 2 mm slice thickness, and one acquisition. A non-imaging CW-CEST sequence with free induction decay (FID) readout and 8-second hard saturation pulse and TR of 10 second was used for phantom imaging. Z-spectra were acquired with RF offsets (Δω) from −10 ppm to 10 ppm. Control images were acquired with RF offsets of 250 ppm. R_1w and MT pool size ratio were obtained using a selective inversion recovery quantitative MT method (33 (link)). All in vivo and phantom imaging were performed at 37°C with saturation power of 0.5 μT. Experiments on all animals and phantoms were performed on a Varian 4.7-T magnet, and the reconstituted phospholipids were performed on a Varian 9.4-T magnet.

McCune S.L., Reilly M.P., Chomo M.J., Asakura T, & Townes T.M. (1994). Recombinant human hemoglobins designed for gene therapy of sickle cell disease.. Proceedings of the National Academy of Sciences of the United States of America, 91(21), 9852-9856.

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Ex vivo MRI of Squirrel Monkey Brains

Cited 6 times

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Ex vivo experiments were performed on six squirrel monkeys. The brains were perfusion fixed with 4% paraformaldehyde preceded by rinse with physiological saline. Brains were then removed and immersed for 3 weeks in phosphate-buffered saline (PBS) medium with 1mM Gd-DTPA in order to reduce longitudinal relaxation times (D’Arceuil et al. 2007 (link)). The brains were then placed in liquid Fomblin (California Vacuum Technology) and scanned on the same Varian 9.4 T magnet. Ex vivo imaging has several experimental advantages including longer scanning times and absence of motion. Together, this allows acquisition of data with higher signal-to-noise ratios and at a higher resolution compared to in vivo studies. We chose to include ex vivo templates because of their significantly increased contrast, and the additional value of the use of ex vivo and subsequent histology as a means to validate MRI techniques and aid image interpretation (Azadbakht et al. 2015 (link); Bastiani et al. 2016 (link); Calabrese et al. 2015 (link); Choe et al. 2012 (link); Knosche et al. 2015 (link); Leergaard et al. 2010 (link); McNab et al. 2009 (link); Schilling et al. 2016 (link)).

Schilling K.G., Gao Y., Stepniewska I., Wu T.L., Wang F., Landman B.A., Gore J.C., Chen L.M, & Anderson A.W. (2017). The VALiDATe29 MRI Based Multi-Channel Atlas of the Squirrel Monkey Brain. Neuroinformatics, 15(4), 321-331.

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Dynamic Contrast-Enhanced MRI Protocol

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MRI was performed every 2 weeks using a 9.4-T magnet (Agilent, Inc., Santa Clara, CA, USA) with a 64 mm transmit/receive volume coil. Animals were anesthetized with a 1.5–2% isoflurane/air mixture during the imaging session, body temperature was maintained at 37.5 ± 0.5°C with an air heater system, and the respiratory rate was monitored to adjust the anesthetic concentration. T1-weighted dynamic contrast-enhanced (DCE)-MRI were obtained after the administration of 25 µmol/kg Gd-EOB-DTPA (Primovist, Bayer Healthcare, Leverkusen, Germany) by intravenous injection after 120 s. The MRI parameters were: (1) T1-weighted DCE-MRIs with TR/TE=70/2.34 ms, flip angle=35°, averages=1, matrix size=96×96, field-of-view (FOV)=50×50 mm² (resolution: 0.52 mm), total scan time=44 min 48 s, and the number of images=400; and (2) T₂* maps with TR/TE=800/2.56 ms, echo=6, flip angle=30°, averages=4, matrix size 128×128, and FOV=50×50 mm² (resolution: 0.39 mm).

Chae Y.J., Heo H., Woo C.W., Kim S.T., Kwon J.I., Choi M.Y., Sung Y.S., Kim K.W., Kim J.K., Choi Y, & Woo D.C. (2022). Preclinical Long-term Magnetic Resonance Imaging Study of Silymarin Liver-protective Effects. Journal of Clinical and Translational Hepatology, 10(6), 1167-1175.

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Dynamic MRI Imaging of Contrast Agents

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MRL was also performed using a 9.4-T magnet (Agilent, Inc., Santa Clara, CA, USA) with a 64-mm transmit/receive volume coil. All animals were maintained under respiratory anesthesia with a 1.5-2% isoflurane/air mixture; body temperature was maintained at 37.5 ± 0.5°C with an air heater system; and the respiratory rate was continuously monitored to adjust the anesthetic concentration. Sequential images of MRL were acquired at 16-min intervals (0, 16, 32, 48, 64, 80, and 94 min) on coronal 3D time-of-flight (TOF) sequence with saturation bands before and after the intradermal injection of contrast agents. The detailed parameters were as follows: TR = 10 ms, TE = 2.54 ms, flip angle = 40°, average = 2, matrix size = 256 × 256 × 192, and field of view = 70 × 70 × 30 mm 3 .

Chae Y.J., Kim K.W., Kim M.H., Woo C.W., Kim S.T., Kim J.W., Shin T.H., Lee D.W., Kim J.K., Choi Y, & Woo D.C. (2024). Comparison of the Pharmacokinetics of Gadolinium-Based and Iron Oxide-Based Contrast Agents inside the Lymphatic Structure using Magnetic Resonance Lymphangiography. Molecular imaging and biology, 26(4).

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MRI Nanoprobe Bacterial Binding Assay

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The MRI nanoprobe was incubated for 1 h with culture media, S. epidermidis (non-targeting bacteria) and S. aureus (targeting bacteria). Then, the probe was loaded into Wilmad NMR tubes 3-mm diameter at concentrations of 0.03 and 0.07 mM Fe and incubated at 37 °C during MRI scan. MRI scans were carried out in a preclinical 9.4-T magnet (Agilent, Palo Alto, CA, USA) interfaced to Avance III electronics, using a quadrature transmit-receive coil (Bruker, Ettlingen, Germany). T₁ values were estimated from images acquired using the rapid acquisition with relaxation enhancement (RARE) sequence with inversion recovery (IT = 50, 200, 400, 800, 1500, 3000, 5500, 8000, 12,000 ms, TE = 7.0 ms, echo train length 2, data matrix size 128 × 64, field of view 30 × 15 mm², slice thickness = 3 mm, 1 scan).

Periyathambi P., Balian A., Hu Z., Padro D., Hernandez L.I., Uvdal K., Duarte J, & Hernandez F.J. (2021). Activatable MRI probes for the specific detection of bacteria. Analytical and Bioanalytical Chemistry, 413(30), 7353-7362.

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In Vivo MRI of Mice with Gadolinium Contrast

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Animals were anesthetized with 3.5% isoflurane in a mixture with 200 mL/min oxygen and 200 mL/min nitrous oxide and maintained at 1.5%–2% isoflurane inside the magnet. Gadolinium contrast agent (Dotarem, Guerbet, Villepinte, France) (gadoteric acid, 279.3 mg/mL, 0.5 mmol/mL) was administered intraperitoneally (100 μg/20 g) in the left abdominal quadrant 55–65 min before MRI. The induction chamber was kept warm at 37°C. Inside the magnet, the respiratory rate of the animal was monitored (SA Instruments, New York, USA) and the body temperature was maintained using a Lauda Rc6 CS recirculating water bath (Köningshofen, Germany).
MRI was performed as previously described20 22 23 (link) with a 9.4 T magnet (Agilent, Palo Alto, USA) using Avance III electronics (Bruker, Ettlingen, Germany). The system is equipped with a 12 cm inner diameter gradient system having a maximum gradient strength of 670 mT/m. The animals were imaged using a quadrature transmit/receive cryoprobe (Bruker). T1-weighted three-dimensional (3D) images were acquired with a gradient echo 3D sequence; repetition time TR: 11 ms, echo time TE: 3.695 ms, number of averages: 2, data matrix size 220×220×147 pixels, field of view 15×15×10 mm³. Images were reconstructed by zero filling to increase the apparent resolution of the image to a matrix size of 440×440×294 pixels and an apparent pixel resolution of 0.034 mm.

Pålbrink A.K., Kopietz F., Morén B., In 't Zandt R., Kalinec F., Stenkula K., Göransson O., Holm C., Magnusson M, & Degerman E. (2020). Inner ear is a target for insulin signaling and insulin resistance: evidence from mice and auditory HEI-OC1 cells. BMJ Open Diabetes Research & Care, 8(1), e000820.

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