Magnetom skyra mri scanner

Manufactured by Siemens

Sourced in Germany

The MAGNETOM Skyra MRI scanner is a magnetic resonance imaging (MRI) system manufactured by Siemens. It is designed to provide high-quality imaging for clinical diagnostics. The core function of the MAGNETOM Skyra is to generate detailed images of the body's internal structures using strong magnetic fields and radio waves.

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Lab products found in correlation

20 channel phase array head coil, by Siemens (1 mentions) 1.41 t minispec mq 60 nmr analyzer, by Bruker (1 mentions)

Close spelling variants of this product

MAGNETOM Skyra 3T MRI scanner MAGNETOM Skyra 3 Tesla MRI scanner 3T MAGNETOM Skyra whole-body MRI scanner Magnetom Skyra 3.0T MRI scanner MAGNETOM Skyra 3-Tesla whole-body MRI Scanner MAGNETOM Skyra scanner Skyra MRI scanner MAGNETOM Skyra Skyra MRI Skyra scanner

6 protocols using magnetom skyra mri scanner

High-Resolution Brain Imaging with MP2RAGE and TOF-MRA

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A 3.0-Tesla MAGNETOM Skyra MRI scanner (Siemens AG, Erlangen, Germany) equipped with a 20-channel phase-array head coil was used to acquire 3-dimensional high-resolution structural images. Every subject was placed in a supine position and was asked to keep his or her head as still as possible during MRI acquisition. The following magnetization-prepared 2 rapid gradient echoes (MP2RAGE) acquisition parameters were used: repetition time (TR) = 4000 ms; echo time (TE) = 2.98 ms; inversion time (TI) = 0 ms; flip angle = 0°; field of view (FOV) = 256 × 256 mm; slice thickness = 1 mm; number of slices = 176; and voxel size = 1 mm × 1 mm × 1 mm.
An additional 3-dimensional time-of-flight MRA was carried out after the structural scan using the following parameters: TR = 20 ms; TE = 3.43 ms; FA = 18°; FOV = 640 × 580 mm; and slice thickness = 0.5 mm.

Zuo Z., Li G., Chen Y., Qiao P., Zhu J., Wang P., Wu F., Yu H., Jiang Y., Yang J., Li G., Jiang R, & Du F. (2023). Atrophy in subcortical gray matter in adult patients with moyamoya disease. Neurological Sciences, 44(5), 1709-1717.

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Multimodal Imaging of Gd-Au Nanocomposites

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For in vivo FI, 200 μL Gd–Au NCs or Gd-Au-NC-GPC-1 (Au: 37 μM/kg) was intravenously injected into each COLO-357 tumor-bearing mouse (n=3). Then, fluorescence images were acquired at different time points before (0 minute) and after (10, 30, and 40 minutes) tail vein injection. FI was performed using an IVIS Lumina II (Hopkinton, MA, USA). The excitation wavelength of filter was 535 nm, and the emission wavelength was 670 nm. In addition, relative fluorescence intensity of the tumor region was measured and expressed as mean ± SD.
For in vivo MRI, 200 μL Gd–Au NCs or Gd-Au-NC-GPC-1 (Gd: 50 μM/kg) was intravenously injected into each COLO-357 tumor-bearing mouse (n=3). Then, MR images were obtained at different time points before (0 minute) and after (10, 30, 60, and 120 minutes) tail vein injection. MRI was performed using a 3.0 T MAGNETOM Skyra MRI scanner (Siemens) using T1-weighted sequence (Mapping, TR/TE =6.83/2.26 ms, thickness =2 mm). In addition, the relative MR intensity of the tumor region was measured and expressed as mean ± SD.

Huang X., Fan C., Zhu H., Le W., Cui S., Chen X., Li W., Zhang F., Huang Y., Sh D., Cui Z., Shao C, & Chen B. (2018). Glypican-1-antibody-conjugated Gd–Au nanoclusters for FI/MRI dual-modal targeted detection of pancreatic cancer. International Journal of Nanomedicine, 13, 2585-2599.

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Gd-Au-NC-GPC-1 Relaxivity and MRI Evaluation

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The longitudinal (T1) and transverse (T2) relaxation times of Gd-Au-NC-GPC-1 were evaluated by using a 1.41 T minispec mq60 NMR Analyzer (Bruker Optik GmbH, Ettlingen, Germany) at 37°C. Relaxivity values of r1 and r2 were calculated by fitting the 1/T1 and 1/T2 relaxation time (s⁻¹) versus the Gd concentration (mM) curves.
For in vitro MRI, COLO-357 and 293T cells (2×10⁶) were treated with various concentrations of Gd-Au-NC-GPC-1 at 37°C for 2 hours. The cells were then washed 3 times with PBS and harvested by trypsinization for 3 minutes. After centrifugation at 1,000 rpm for 5 minutes, the cells were resuspended in 20 μL PBS in an Eppendorf Tube^® (Axygen, CA, USA). Magnetic resonance images were acquired using a 3.0 T MAGNETOM Skyra MRI scanner (Siemens, Erlangen, Germany) using T1-weighted sequence (Mapping, repetition time/echo time [TR/TE] =6.83/2.26 ms, thickness =2 mm).

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High-Resolution T1-Weighted Brain MRI

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A 3 T MAGNETOM Skyra MRI scanner (Siemens Healthcare, Germany) with a 32-channel head coil (AMI center, Aalto University, Espoo, Finland; duration 30 min) was used. High-resolution magnetization prepared rapid acquisition gradient-recalled T1 images were obtained (176 slices, slice thickness 1 mm, flip angle = 7°, TR = 2530 ms, TE = 3.3 ms, voxel size = 1.0 × 1.0 × 1.0 mm³). A physician checked the MRIs for incidental findings.

Kujala T., Sihvonen A.J., Thiede A., Palo-oja P., Virtala P., Numminen J, & Laasonen M. (2021). Voxel and surface based whole brain analysis shows reading skill associated grey matter abnormalities in dyslexia. Scientific Reports, 11, 10862.

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Quantifying Pancreatic Fat Deposition

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All study participants underwent abdominal MRI on a 3.0 Tesla MAGNETOM Skyra MRI Scanner (Siemens, Erlangen, Germany), specifically for the purpose of the ARIES project. The MRI acquisition parameters were detailed elsewhere [16] . The technique used to quantify IPFD was described in detail elsewhere [17] . In brief, 3 regions of interest were placed in the head, body, and tail regions of the pancreas of 2 candidate slices. A thresholding range of 1-20% was applied to avoid nonparenchymal tissue within the selected regions of interest. The average measurement of the 2 candidate slices was used for statistical analyses. The ratio of visceral-to-subcutaneous (V/S) fat volume was also calculated as described elsewhere [18] . Two raters, blinded to the participant groups, independently carried out the measurements of IPFD, subcutaneous fat volume, and visceral fat volume. The inter-rater reliability of the MRI measurements was determined by intraclass correlation coefficients [19] . Statistical analyses used the average values of 2 independent MRI measurements for each fat depot.

Nguyen N.N., Singh R.G, & Petrov M.S. (2022). Association between Intrapancreatic Fat Deposition and the Leptin/Ghrelin Ratio in the Fasted and Postprandial States. Annals of nutrition & metabolism, 78(1).

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Early-stage Parkinson's Disease Neuroimaging

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78 newly diagnosed patients with PD were recruited from the third hospital of Mianyang from June 1, 2016 to December 31, 2019. A clinical diagnosis of early PD was made according to the UK Brain Bank criteria [7] . None of the patients had ever taken medication for PD. We collected demographic data (age, gender and education level), medical history and clinical details (age at onset and disease duration). Disease severity was evaluated by Hoehn & Yahr stage and motor disability was assessed with the Movement Disorders Society-revised Unified Parkinson's Disease Rating Scale (MDS-UPDRS) parts III8. Lacunae and white matter lesions were evaluated using a previously recommended standard [24, 25] . All MRI scans were performed on a 3.0 Tesla Magnetom Skyra MRI scanner (Siemens Medical Solutions, Erlangen, Germany) [26] .
Excluded from the study were patients with: (1) neurological abnormalities related to atypical and secondary Parkinsonism;
(2) current intake of medications known to influence autonomic functions; (3) multiple system atrophy; (4) corticobasal degeneration; (5) a history of cardiopathy or peripheral neuropathy [17] .

Lai Y. (2021). Association of Cognitive Dysfunction with Cardiovascular Autonomic Nerve Abnormalities in Early Parkinson Disease. Psychology and Behavioral Science International Journal, 17(1).

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