HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008
|
|
- Rodney Parker
- 6 years ago
- Views:
Transcription
1 MIT OpenCourseWare HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008 For information about citing these materials or our Terms of Use, visit:
2 HST.583: Functional Magnetic Resonance Imaging: Data Acquisition and Analysis, Fall 2008 Harvard-MIT Division of Health Sciences and Technology Course Director: Dr. Randy Gollub. 2. T, T2 and T2* Measurements Background To calculate T values of the tissue we will be using an inversion recovery turbo spin echo sequence. We will be sampling the magnetization as a function of the inversion time (TI). The observed signal intensity is given by the following equation: S(t) [ 2exp( TI /T)] () To obtain the transverse relaxation time, T2, values in the brain a series of spin echo images will be acquired by stepping through a range of TEs. The image intensity is given by the following equation: S(t) exp( TE /T 2) (2) T2star (T2*) is the time constant that describes the decay of the transverse magnetization including local magnetic field inhomogeneities. T2* is an important relaxation time for functional studies because it is related to the amount of deoxygenated hemoglobin present in the brain. To determine the T2* values in gray, white matter and CSF, we will be using a gradient echo sequence and the signal is described by: S(t) exp( TE / T 2*) (3)
3 Experiments In this exercise we will acquire and evaluate human data in order to characterize T, T2 and T2* values in brain tissue compartments. Various sequences will be used with the imaging parameters manipulated so that they provide the appropriate contrast weightings. T measurements Acqusition: Total scan time: 5m 38sec A. Inversion Recovery Turbo Spin Echo (tse_ir) sequence with TR=3000ms, FOV=240x240, matrix=96x28, repeated for multiple inversion times TI=200, 300, 400, 500, 600, 700, 800, 000, 300, 500, 700, 2000, 2200 ms.. Load all the images on the viewer. 2. Draw ROIs in gray matter areas. 3. Record the mean signal values in Table for each inversion time and ROI. 4. Repeat steps -3 for regions of white matter and CSF. Lab Question 6 : Draw the measured signal as a function of inversion time for each of the tissue compartments. Calculate the T for gray, white matter and CSF by fitting Eq. () to your data. Hint: you will need to use a nonlinear fitting function such as nlinfit in matlab to accomplish this. T2 measurements Acqusition: Total scan time: 9m 42sec B. SE sequence with TR=4000ms, FOV=220x220, matrix=92x92, 8 echo times in a range between 4.3ms and 4.4ms and inter-echo spacing 4.3 ms. 5. Load all the images on the viewer. 6. Draw ROIs in gray matter areas. 7. Record the mean signal values in Table 2 for each echo time and ROI. 8. Repeat steps -3 for regions of white matter and CSF. Lab Question 7 : Draw the measured signal as a function of echo time for each of the tissue compartments. Calculate the T2 for gray, white matter and CSF by fitting Eq. (2) to your data. T2* measurements Acqusition: Total scan time: sec C. 2D FLASH sequence with TR=00msec, FOV=256x256, matrix=28x28, and multi contrast with echo times TE=6, 0, 5, 20, 30, 50, 70, 80 msec. 9. Load all the images on the viewer.
4 0. Draw ROIs in gray matter areas.. Record the mean signal values in Table 3 for each echo time and ROI. 2. Repeat steps -3 for regions of white matter and CSF. Lab Question 8 : Draw the measured signal as a function of echo time for each of the tissue compartments. Calculate the T2* of gray and white matter and CSF by fitting Eq. (3) to your data. Lab Question 9 : According to your measurements how do T2 and T2* compare for the same tissue compartment? Did you expect these findings? Explain why. Table T Measurements TI (ms) Gray White CSF Matter Matter
5 Table 2 T2 Measurements TE (ms) Gray White CSF Matter Matter Table 3 T2* Measurements TE (ms) Gray White CSF Matter Matter
6 3. Distortion in EPI due to B0 Inhomogeneity Background The echo-planar image (EPI) is distorted due to local field gradients present in the head during imaging. Since the acquisition of k-space data is very asymmetric in EPI, with the readout direction points (kx) collected quickly and the phase encode steps (ky) relatively slowly, the distortion is essentially entirely in the y direction (phase encode direction). The relative distortion between the two directions can be estimated from the relative speed of the acquisition. In kx, at a typical readout BW (say 2.2kHz/pixel or 40kHz in frequency across the 64 pixel image), the dwell time (time between kx samples) is 7.μs. The ky sampling rate is slower because of the zig-zag trajectory, and is about 64 times slower. This gives a sampling spacing of 64 * 7.μs = 0.45ms. We call this.the "echospacing", (esp), of the sequence, the time between gradient echos (acquisition of the kx=0 point). The effective "bandwidth" in the phase encode direction is therefore across the esp image or /64*esp = 34.7Hz/pixel. Therefore a B0 shift which induces a 34.7Hz frequency shift will induce a shift in this region of pixel. The frequency shifts in the "bad susceptibility" regions of the brain are easily in the 00Hz range. Therefore, the principle metric of how distorted the EPI sequence will be is its effective echo-spacing. For conventional echo-planar imaging, this is basically limited by the gradient slew rate and amplitude. Using parallel acceleration such as SENSE or GRAPPA effectively decreases the esp by a factor of the acceleration factor, (i.e. 2 or 3 fold).
7 Experiments In this lab we will acquire images with different effective esp and compare the distortion in the brain. Acquisition : ) epi_esp730: voxel size = 3. x 3. x 3., Matrix size = 64x64, BW=502Hz/px, ESP=0.73ms, effective esp =0.73ms 2) epi_esp460: voxel size = 3. x 3. x 3., Matrix size = 64x64, BW=2520Hz/px, ESP=0.46ms, effective esp =0.46ms 3) epi_esp480_grappa: voxel size = 3. x 3. x 3., Matrix size = 64x64, BW=2520Hz/px, ESP=0.48ms, effective esp =0.46ms Lab Question 0: Estimate the distortion in frontal lobes by measuring distance on the scanner to some reference feature. Plot the distortion in mm as a function of effective esp.
8 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\tse_IR TA: 0:26 PAT: Voxel size: mm Rel. SNR:.00 SIEMENS: tse Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices Dist. factor 50 % Position R0.7 A0.8 H2.2 T > C-0.3 Phase enc. dir deg Phase oversampling 0 % FoV read 240 mm FoV phase 75.0 % Slice thickness 5.0 mm TR 3000 ms TE 2 ms Averages Concatenations Filter Coil elements HEA;HEP Contrast MTC Magn. preparation TI Freeze suppressed tissue Flip angle Fat suppr. Fat sat. mode Water suppr. Restore magn. Averaging mode Reconstruction Measurements Multiple series Slice-sel. IR 200 ms 80 deg Strong Short term Real Each measurement Resolution Base resolution 28 Phase resolution 00 % Phase partial Fourier Trajectory Cartesian Interpolation PAT mode Matrix Coil Mode Image Filter Distortion Corr. Prescan rmalize rmalize Auto (CP) Raw filter Elliptical filter Geometry Multi-slice mode Series Special sat. System Body HEP HEA Positioning mode MSMA Sagittal Coronal Save uncombined Coil Combine Mode Auto Coil Select REF H 0 mm S - C - T Adaptive Combine Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Tune up V Auto Isocenter 0.00 deg 350 mm 263 mm 350 mm Dark blood Resp. control Inline Subtract Std-Dev-Sag Std-Dev-Cor Std-Dev-Tra Std-Dev-Time MIP-Sag MIP-Cor MIP-Tra MIP-Time Save original images Sequence Introduction Dimension 2D Compensate T2 decay Reduce Motion Sens. Contrasts Bandwidth 30 Hz/Px Flow comp. Allowed delay 0 s Echo spacing.7 ms /+
9 SIEMENS MAGNETOM TrioTim syngo MR B5 Define Turbo factor Turbo factor 5 Echo trains per slice 7 RF pulse type rmal Gradient mode Fast 2/+
10 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\se_mc TA: 9:42 PAT: Voxel size: mm Rel. SNR:.00 SIEMENS: se_mc Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices Dist. factor 00 % Position R0.7 A0.8 H2.2 T > C-0.3 Phase enc. dir deg Phase oversampling 0 % FoV read 220 mm FoV phase 00.0 % Slice thickness 5.0 mm TR 4000 ms TE 4.3 ms TE ms TE ms TE ms TE ms TE ms TE ms TE ms Averages Concatenations Filter Raw filter Coil elements HEA;HEP Contrast MTC Magn. preparation Flip angle Fat suppr. Fat sat. mode Water suppr. Averaging mode Reconstruction Measurements Multiple series 80 deg Strong Resolution Base resolution 92 Phase resolution 00 % Phase partial Fourier 6/8 Interpolation PAT mode Matrix Coil Mode Image Filter Short term Magnitude Each measurement Auto (CP) Distortion Corr. Prescan rmalize rmalize Raw filter Intensity Weak Slope 25 Elliptical filter Geometry Multi-slice mode Series Special sat. System Body HEP HEA Positioning mode MSMA Sagittal Coronal Save uncombined Coil Combine Mode Auto Coil Select REF H 0 mm S - C - T Adaptive Combine Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Tune up V Auto Isocenter 0.00 deg 350 mm 263 mm 350 mm Dark blood Inline Subtract Liver registration Std-Dev-Sag Std-Dev-Cor Std-Dev-Tra Std-Dev-Time MIP-Sag MIP-Cor MIP-Tra MIP-Time Save original images Sequence Introduction Contrasts Bandwidth Allowed delay RF pulse type 3/ Hz/Px 0 s rmal
11 SIEMENS MAGNETOM TrioTim syngo MR B5 Gradient mode Fast 4/+
12 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\T2star_8echos TA: 0: PAT: Voxel size: mm Rel. SNR:.00 SIEMENS: gre Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices Dist. factor 20 % Position R0.7 A0.8 H2.2 T > C-0.3 Phase enc. dir deg Phase oversampling 0 % FoV read 256 mm FoV phase 00.0 % Slice thickness 5.0 mm TR 00 ms TE 6.00 ms TE ms TE ms TE ms TE ms TE ms TE ms TE ms Averages Concatenations Filter Raw filter Coil elements HEA;HEP Contrast MTC Magn. preparation Flip angle Fat suppr. Water suppr. Averaging mode Reconstruction Measurements Multiple series 5 deg Resolution Base resolution 28 Phase resolution 00 % Phase partial Fourier 6/8 Interpolation PAT mode Matrix Coil Mode Image Filter Distortion Corr. Long term Magnitude Each measurement Auto (CP) Prescan rmalize rmalize Raw filter Intensity Weak Slope 25 Elliptical filter Geometry Multi-slice mode Series Sequential Saturation mode Special sat. Standard System Body HEP HEA Positioning mode MSMA Sagittal Coronal Save uncombined Coil Combine Mode Auto Coil Select REF H 0 mm S - C - T Adaptive Combine Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Segments Tune up V Auto Isocenter 0.00 deg 350 mm 263 mm 350 mm Dark blood Resp. control Inline Subtract Liver registration Std-Dev-Sag Std-Dev-Cor Std-Dev-Tra Std-Dev-Time MIP-Sag MIP-Cor MIP-Tra MIP-Time Save original images 5/+ Wash - In Wash - Out TTP
13 SIEMENS MAGNETOM TrioTim syngo MR B5 PEI MIP - time Sequence Introduction Dimension 2D Phase stabilisation Asymmetric echo Contrasts 8 Bandwidth 300 Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Bandwidth Hz/Px Flow comp. Flow comp. 2 Flow comp. 3 Flow comp. 4 Flow comp. 5 Flow comp. 6 Flow comp. 7 Flow comp. 8 Readout mode Bipolar Allowed delay 0 s RF pulse type Gradient mode Excitation RF spoiling rmal Fast Slice-sel. 6/+
14 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\epi_esp730 TA: 2.0 s PAT: Voxel size: mm Rel. SNR:.00 USER: ep2d_bold_mgh_pro_tb Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices 9 Dist. factor 67 % Position R0.3 A.0 F2. T > C-0.4 Phase enc. dir deg Phase oversampling 0 % FoV read FoV phase 00.0 % Slice thickness 3.0 mm TR 2000 ms TE 30 ms Averages Concatenations Filter Coil elements HEA;HEP Contrast MTC Flip angle Fat suppr. Averaging mode Reconstruction Measurements Delay in TR Multiple series 90 deg Fat sat. Long term Magnitude 0 ms Resolution Base resolution 64 Phase resolution 00 % Phase partial Fourier Interpolation PAT mode Matrix Coil Mode Distortion Corr. Prescan rmalize Raw filter Elliptical filter Hamming Geometry Multi-slice mode Series Special sat. Auto (CP) System Body HEP HEA Positioning mode MSMA Sagittal Coronal Coil Combine Mode Auto Coil Select FIX H 0 mm S - C - T Sum of Squares Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Standard V Auto R0.3 A.0 F2. T > C deg 45 mm BOLD GLM Statistics Dynamic t-maps Starting ignore meas 0 Ignore after transition 0 Model transition states Temp. highpass filter Threshold 4.00 Paradigm size Meas Baseline Motion correction Spatial filter Sequence Introduction Bandwidth Free echo spacing Echo spacing 7/+ 502 Hz/Px 0.73 ms EPI factor RF pulse type Gradient mode 64 rmal Fast Dummy Scans 0
15 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\epi_esp460 TA: 2.0 s PAT: Voxel size: mm Rel. SNR:.00 USER: ep2d_bold_mgh_pro_tb Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices 9 Dist. factor 67 % Position R0.3 A.0 F2. T > C-2.5 Phase enc. dir deg Phase oversampling 0 % FoV read FoV phase 00.0 % Slice thickness 3.0 mm TR 2000 ms TE 30 ms Averages Concatenations Filter Coil elements HEA;HEP Contrast MTC Flip angle Fat suppr. Averaging mode Reconstruction Measurements Delay in TR Multiple series 90 deg Fat sat. Long term Magnitude 0 ms Resolution Base resolution 64 Phase resolution 00 % Phase partial Fourier Interpolation PAT mode Matrix Coil Mode Distortion Corr. Prescan rmalize Raw filter Elliptical filter Hamming Geometry Multi-slice mode Series Special sat. Auto (CP) System Body HEP HEA Positioning mode MSMA Sagittal Coronal Coil Combine Mode Auto Coil Select FIX H 0 mm S - C - T Sum of Squares Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Standard V Auto R0.3 A.0 F2. T > C deg 45 mm BOLD GLM Statistics Dynamic t-maps Starting ignore meas 0 Ignore after transition 0 Model transition states Temp. highpass filter Threshold 4.00 Paradigm size Meas Baseline Motion correction Spatial filter Sequence Introduction Bandwidth Free echo spacing Echo spacing 8/ Hz/Px 0.46 ms EPI factor RF pulse type Gradient mode 64 rmal Fast Dummy Scans 0
16 SIEMENS MAGNETOM TrioTim syngo MR B5 \\USER\INVESTIGATORS\HST_583\Physics2\epi_esp480_grappa2 TA: 8.0 s PAT: 2 Voxel size: mm Rel. SNR:.00 USER: ep2d_bold_mgh_pro_tb Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto store images Load to stamp segments Load images to graphic segments Auto open inline display AutoAlign Spine Start measurement without further preparation Wait for user to start Start measurements single Routine Slice group Slices 9 Dist. factor 67 % Position R0.3 A.0 F2. T > C-2.5 Phase enc. dir deg Phase oversampling 0 % FoV read FoV phase 00.0 % Slice thickness 3.0 mm TR 2000 ms TE 30 ms Averages Concatenations Filter Coil elements HEA;HEP Contrast MTC Flip angle Fat suppr. Averaging mode Reconstruction Measurements Delay in TR Multiple series 90 deg Fat sat. Long term Magnitude 0 ms Resolution Base resolution 64 Phase resolution 00 % Phase partial Fourier Interpolation PAT mode Accel. factor PE Ref. lines PE Matrix Coil Mode Reference scan mode Distortion Corr. Prescan rmalize Raw filter Elliptical filter Hamming Geometry Multi-slice mode GRAPPA 2 32 Auto (Triple) Separate Series Special sat. System Body HEP HEA Positioning mode MSMA Sagittal Coronal Coil Combine Mode Auto Coil Select FIX H 0 mm S - C - T Sum of Squares Default Shim mode Adjust with body coil Confirm freq. adjustment Assume Silicone Ref. amplitude H Adjustment Tolerance Adjust volume Position Physio st Signal/Mode Standard V Auto R0.3 A.0 F2. T > C deg 45 mm BOLD GLM Statistics Dynamic t-maps Starting ignore meas 0 Ignore after transition 0 Model transition states Temp. highpass filter Threshold 4.00 Paradigm size Meas Baseline Motion correction Spatial filter Sequence Introduction Bandwidth Free echo spacing Echo spacing 9/ 2520 Hz/Px 0.48 ms EPI factor RF pulse type Gradient mode 64 rmal Fast Dummy Scans 0
HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationHST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2006
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2006 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationCOBRE Scan Information
COBRE Scan Information Below is more information on the directory structure for the COBRE imaging data. Also below are the imaging parameters for each series. Directory structure: var/www/html/dropbox/1139_anonymized/human:
More informationSIEMENS MAGNETOM Avanto syngo MR B15
\\USER\INVESTIGATORS\Ravi\ADNI-Subject\Localizer TA: 0:10 PAT: Voxel size: 1.9 1.5 8.0 mm Rel. SNR: 1.00 SIEMENS: gre Properties Prio Recon Before measurement After measurement Load to viewer Inline movie
More informationSIEMENS MAGNETOM Avanto syngo MR B15
\\USER\INVESTIGATORS\Ravi\ADNI-phantom\QC Phantom-Localizer TA: 0:10 PAT: Voxel size: 1.9 1.5 8.0 mm Rel. SNR: 1.00 SIEMENS: gre Properties Prio Recon Before measurement After measurement Load to viewer
More informationSIEMENS MAGNETOM Verio syngo MR B17
\\USER\Dr. Behrmann\routine\Ilan\ep2d_bold_PMU_resting TA: 8:06 PAT: Voxel size: 3.03.03.0 mm Rel. SNR: 1.00 USER: ep2d_bold_pmu Properties Special sat. Prio Recon System Before measurement Body After
More informationSIEMENS MAGNETOM Verio syngo MR B15V
\\USER\ZAHID_RESEARCH\MS\No Name\3D SWI TA: 6:39 PAT: 2 Voxel size: 1.0 0.5 2.0 mm Rel. SNR: 1.00 SIEMENS: gre Properties Prio Recon Before measurement After measurement Load to viewer Inline movie Auto
More informationSIEMENS MAGNETOM Skyra syngo MR D13
Page 1 of 8 SIEMENS MAGNETOM Skyra syngo MR D13 \\USER\CIND\StudyProtocols\PTSA\*dm_ep2d_mono70_b0_p2_iso2.0 TA:1:05 PAT:2 Voxel size:2.0 2.0 2.0 mm Rel. SNR:1.00 :epse Properties Routine Prio Recon Load
More informationSIEMENS MAGNETOM TrioTim syngo MR B17
\\USER\KNARRGROUP\MultiBand\LavretskyMultiBand\trufi localizer 3-plane TA: 5.1 s PAT: Voxel size: 1.2 1.2 5. Rel. SNR: 1.00 SIEMENS: trufi Load to stamp Slice group 1 Slices 1 Dist. factor 20 % Phase enc.
More informationSOP: Brain MRI Inital version Gorm Greisen. CONTENT 1.0 Timing of Brain MRI Informed consent...1
SOP: Brain MRI Author(s) Date Changes Approved by Cornelia Hagmann Manon Benders Anne Mette Plomgaard 23.09.2012 1.0 Inital version Gorm Greisen CONTENT 1.0 Timing of Brain MRI...1 2.0 Informed consent...1
More informationLab Location: MRI, B2, Cardinal Carter Wing, St. Michael s Hospital, 30 Bond Street
Lab Location: MRI, B2, Cardinal Carter Wing, St. Michael s Hospital, 30 Bond Street MRI is located in the sub basement of CC wing. From Queen or Victoria, follow the baby blue arrows and ride the CC south
More informationSiemens AG, Healthcare Sector. syngo MR D13 0. Supplement - Parameters and image text 0.
Siemens AG, Healthcare Sector 0 0 n.a. English Cs2 syngo Neuro Operator MR-05014 630 05/2010 01 02 Informatik, Manual D11 Cape syngo MR D13 0.0 Supplement - Parameters and image text 0. syngo MR D13 0.
More informationSIEMENS MAGNETOM Symphony syngo MR A30
\\USER\ADNI STUDY\MAIN PROTOCOL\HUMAN PROTOCOL\localizer Scan Time: 9.2 [s] Voxel size: 2.2 1.1 10.0 [mm] Rel. SNR: 1.00 SIEMENS: gre Slice group 1 Slice group 2 Slice group 3 280 [mm] 10 [mm] 20 [ms]
More informationPhilips MRI Protocol Dump Created on Comment Software Stream
Page 1 of 5 Philips MRI Protocol Dump Created on 2/17/2011 4:11:01 PM Comment Created by ExamCard_to_XML with inputs: "J:\ADNI GO - ADNI 2 Phantom5.ExamCard" on system (BU SCHOOL OF MEDICINE :: 192.168.71.10)
More informationMRI Physics II: Gradients, Imaging
MRI Physics II: Gradients, Imaging Douglas C., Ph.D. Dept. of Biomedical Engineering University of Michigan, Ann Arbor Magnetic Fields in MRI B 0 The main magnetic field. Always on (0.5-7 T) Magnetizes
More informationADNI, ADNI_QH, SURVEY. Geometry. connection
ADNI, ADNI_QH, SURVEY Geometry Coil selection = Head connection = d Multi coil Homogeneity correction ne FOV (mm) = 250.00 RFOV (%) = 100.00 Foldover suppression Matrix scan = 256 reconstruction = 256
More informationDiffusion MRI Acquisition. Karla Miller FMRIB Centre, University of Oxford
Diffusion MRI Acquisition Karla Miller FMRIB Centre, University of Oxford karla@fmrib.ox.ac.uk Diffusion Imaging How is diffusion weighting achieved? How is the image acquired? What are the limitations,
More informationCHAPTER 9: Magnetic Susceptibility Effects in High Field MRI
Figure 1. In the brain, the gray matter has substantially more blood vessels and capillaries than white matter. The magnified image on the right displays the rich vasculature in gray matter forming porous,
More information(a Scrhon5 R2iwd b. P)jc%z 5. ivcr3. 1. I. ZOms Xn,s. 1E IDrAS boms. EE225E/BIOE265 Spring 2013 Principles of MRI. Assignment 8 Solutions
EE225E/BIOE265 Spring 2013 Principles of MRI Miki Lustig Assignment 8 Solutions 1. Nishimura 7.1 P)jc%z 5 ivcr3. 1. I Due Wednesday April 10th, 2013 (a Scrhon5 R2iwd b 0 ZOms Xn,s r cx > qs 4-4 8ni6 4
More informationModule 4. K-Space Symmetry. Review. K-Space Review. K-Space Symmetry. Partial or Fractional Echo. Half or Partial Fourier HASTE
MRES 7005 - Fast Imaging Techniques Module 4 K-Space Symmetry Review K-Space Review K-Space Symmetry Partial or Fractional Echo Half or Partial Fourier HASTE Conditions for successful reconstruction Interpolation
More informationSlide 1. Technical Aspects of Quality Control in Magnetic Resonance Imaging. Slide 2. Annual Compliance Testing. of MRI Systems.
Slide 1 Technical Aspects of Quality Control in Magnetic Resonance Imaging Slide 2 Compliance Testing of MRI Systems, Ph.D. Department of Radiology Henry Ford Hospital, Detroit, MI Slide 3 Compliance Testing
More informationA Virtual MR Scanner for Education
A Virtual MR Scanner for Education Hackländer T, Schalla C, Trümper A, Mertens H, Hiltner J, Cramer BM Hospitals of the University Witten/Herdecke, Department of Radiology Wuppertal, Germany Purpose A
More informationMR Advance Techniques. Vascular Imaging. Class III
MR Advance Techniques Vascular Imaging Class III 1 Vascular Imaging There are several methods that can be used to evaluate the cardiovascular systems with the use of MRI. MRI will aloud to evaluate morphology
More informationScan Acceleration with Rapid Gradient-Echo
Scan Acceleration with Rapid Gradient-Echo Hsiao-Wen Chung ( 鍾孝文 ), Ph.D., Professor Dept. Electrical Engineering, National Taiwan Univ. Dept. Radiology, Tri-Service General Hospital 1 of 214 The Need
More informationOrthopedic MRI Protocols. Philips Panorama HFO
Orthopedic MRI Protocols Philips Panorama HFO 1 2 Prepared in collaboration with Dr. John F. Feller, Medical Director of Desert Medical Imaging, Palm Springs, CA. Desert Medical Imaging will provide the
More informationApplications Guide for Interleaved
Applications Guide for Interleaved rephase/dephase MRAV Authors: Yongquan Ye, Ph.D. Dongmei Wu, MS. Tested MAGNETOM Systems : 7TZ, TRIO a Tim System, Verio MR B15A (N4_VB15A_LATEST_20070519) MR B17A (N4_VB17A_LATEST_20090307_P8)
More informationNew Technology Allows Multiple Image Contrasts in a Single Scan
These images were acquired with an investigational device. PD T2 T2 FLAIR T1 MAP T1 FLAIR PSIR T1 New Technology Allows Multiple Image Contrasts in a Single Scan MR exams can be time consuming. A typical
More informationWhite Pixel Artifact. Caused by a noise spike during acquisition Spike in K-space <--> sinusoid in image space
White Pixel Artifact Caused by a noise spike during acquisition Spike in K-space sinusoid in image space Susceptibility Artifacts Off-resonance artifacts caused by adjacent regions with different
More informationADNI GO - ADNI 2 Human7 (9) 38:30.1
Philips RI Protocol Dump Create on 11/25/2013 11:40:24 A Comment Create by ExamCar_to_XL with inputs: "K:\ADNI GO - ADNI 2 Human7.ExamCar" on system (BU SCHOOL OF EDICINE :: 192.168.71.10) Software Stream
More informationFast Imaging UCLA. Class Business. Class Business. Daniel B. Ennis, Ph.D. Magnetic Resonance Research Labs. Tuesday (3/7) from 6-9pm HW #1 HW #2
Fast Imaging Daniel B. Ennis, Ph.D. Magnetic Resonance Research Labs Class Business Tuesday (3/7) from 6-9pm 6:00-7:30pm Groups Avanto Sara Said, Yara Azar, April Pan Skyra Timothy Marcum, Diana Lopez,
More informationMRI image formation 8/3/2016. Disclosure. Outlines. Chen Lin, PhD DABR 3. Indiana University School of Medicine and Indiana University Health
MRI image formation Indiana University School of Medicine and Indiana University Health Disclosure No conflict of interest for this presentation 2 Outlines Data acquisition Spatial (Slice/Slab) selection
More informationRole of Parallel Imaging in High Field Functional MRI
Role of Parallel Imaging in High Field Functional MRI Douglas C. Noll & Bradley P. Sutton Department of Biomedical Engineering, University of Michigan Supported by NIH Grant DA15410 & The Whitaker Foundation
More informationMRI. When to use What sequences. Outline 2012/09/19. Sequence: Definition. Basic Principles: Step 2. Basic Principles: Step 1. Govind Chavhan, MD
MRI When to use What sequences Govind Chavhan, MD Assistant Professor and Staff Radiologist The Hospital For Sick Children, Toronto Planning Acquisition Post processing Interpretation Patient history and
More informationFunctional MRI. Jerry Allison, Ph. D. Medical College of Georgia
Functional MRI Jerry Allison, Ph. D. Medical College of Georgia BOLD Imaging Technique Blood Oxygen Level Dependent contrast can be used to map brain function Right Hand Motor Task Outline fmri BOLD Contrast
More informationM R I Physics Course
M R I Physics Course Multichannel Technology & Parallel Imaging Nathan Yanasak, Ph.D. Jerry Allison Ph.D. Tom Lavin, B.S. Department of Radiology Medical College of Georgia References: 1) The Physics of
More informationHST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationMidterm Review
Midterm Review - 2017 EE369B Concepts Noise Simulations with Bloch Matrices, EPG Gradient Echo Imaging 1 About the Midterm Monday Oct 30, 2017. CCSR 4107 Up to end of C2 1. Write your name legibly on this
More informationHST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationSupplementary methods
Supplementary methods This section provides additional technical details on the sample, the applied imaging and analysis steps and methods. Structural imaging Trained radiographers placed all participants
More informationFollowing on from the two previous chapters, which considered the model of the
Chapter 5 Simulator validation Following on from the two previous chapters, which considered the model of the simulation process and how this model was implemented in software, this chapter is concerned
More informationPage 1 of 9. Protocol: adult_other_adni3basichumanprotocol25x_ _ _1. 3 Plane Localizer. 3 Plane Localizer PATIENT POSITION
3 Localizer FOV 26.0 Slice Thickness 5.0 Slice Spacing 0.0 Freq 256 Phase 128 3-PLANE 3 Localizer Unswap Phase Correction Gradient Echo Imaging Options Seq, Fast Recon All Images 3 Localizer Pause / SCIC
More informationExam 8N080 - Introduction MRI
Exam 8N080 - Introduction MRI Friday January 23 rd 2015, 13.30-16.30h For this exam you may use an ordinary calculator (not a graphical one). In total there are 6 assignments and a total of 65 points can
More informationFmri Spatial Processing
Educational Course: Fmri Spatial Processing Ray Razlighi Jun. 8, 2014 Spatial Processing Spatial Re-alignment Geometric distortion correction Spatial Normalization Smoothing Why, When, How, Which Why is
More informationLucy Phantom MR Grid Evaluation
Lucy Phantom MR Grid Evaluation Anil Sethi, PhD Loyola University Medical Center, Maywood, IL 60153 November 2015 I. Introduction: The MR distortion grid, used as an insert with Lucy 3D QA phantom, is
More informationBasic fmri Design and Analysis. Preprocessing
Basic fmri Design and Analysis Preprocessing fmri Preprocessing Slice timing correction Geometric distortion correction Head motion correction Temporal filtering Intensity normalization Spatial filtering
More informationField Maps. 1 Field Map Acquisition. John Pauly. October 5, 2005
Field Maps John Pauly October 5, 25 The acquisition and reconstruction of frequency, or field, maps is important for both the acquisition of MRI data, and for its reconstruction. Many of the imaging methods
More informationHead motion in diffusion MRI
Head motion in diffusion MRI Anastasia Yendiki HMS/MGH/MIT Athinoula A. Martinos Center for Biomedical Imaging 11/06/13 Head motion in diffusion MRI 0/33 Diffusion contrast Basic principle of diffusion
More informationMR-Encephalography (MREG)
MR-Encephalography (MREG) C2P package Version 2.0 For SIEMENS Magnetom Verio/TRIO/Skyra/Prisma Installation and User s Guide NUMARIS/4 VB17, VD11, VD13 Jakob Assländer Pierre LeVan, Ph.D. 10.09.2014 Magnetic
More informationsurface Image reconstruction: 2D Fourier Transform
2/1/217 Chapter 2-3 K-space Intro to k-space sampling (chap 3) Frequenc encoding and Discrete sampling (chap 2) Point Spread Function K-space properties K-space sampling principles (chap 3) Basic Contrast
More informationSPM8 for Basic and Clinical Investigators. Preprocessing. fmri Preprocessing
SPM8 for Basic and Clinical Investigators Preprocessing fmri Preprocessing Slice timing correction Geometric distortion correction Head motion correction Temporal filtering Intensity normalization Spatial
More informationDynamic Contrast enhanced MRA
Dynamic Contrast enhanced MRA Speaker: Yung-Chieh Chang Date : 106.07.22 Department of Radiology, Taichung Veterans General Hospital, Taichung, Taiwan 1 Outline Basic and advanced principles of Diffusion
More informationParallel Imaging. Marcin.
Parallel Imaging Marcin m.jankiewicz@gmail.com Parallel Imaging initial thoughts Over the last 15 years, great progress in the development of pmri methods has taken place, thereby producing a multitude
More informationGE Healthcare CLINICAL GALLERY. Discovery * MR750w 3.0T. This brochure is intended for European healthcare professionals.
GE Healthcare CLINICAL GALLERY Discovery * MR750w 3.0T This brochure is intended for European healthcare professionals. NEURO PROPELLER delivers high resolution, motion insensitive imaging in all planes.
More informationSingle Breath-hold Abdominal T 1 Mapping using 3-D Cartesian Sampling and Spatiotemporally Constrained Reconstruction
Single Breath-hold Abdominal T 1 Mapping using 3-D Cartesian Sampling and Spatiotemporally Constrained Reconstruction Felix Lugauer 1,3, Jens Wetzl 1, Christoph Forman 2, Manuel Schneider 1, Berthold Kiefer
More informationEPI Data Are Acquired Serially. EPI Data Are Acquired Serially 10/23/2011. Functional Connectivity Preprocessing. fmri Preprocessing
Functional Connectivity Preprocessing Geometric distortion Head motion Geometric distortion Head motion EPI Data Are Acquired Serially EPI Data Are Acquired Serially descending 1 EPI Data Are Acquired
More informationFunctional MRI in Clinical Research and Practice Preprocessing
Functional MRI in Clinical Research and Practice Preprocessing fmri Preprocessing Slice timing correction Geometric distortion correction Head motion correction Temporal filtering Intensity normalization
More informationACQUIRING AND PROCESSING SUSCEPTIBILITY WEIGHTED IMAGING (SWI) DATA ON GE 3.0T
ACQUIRING AND PROCESSING SUSCEPTIBILITY WEIGHTED IMAGING (SWI) DATA ON GE 3.0T Revision date: 12/13/2010 Overview Susceptibility Weighted Imaging (SWI) is a relatively new data acquisition and processing
More informationClinical Importance. Aortic Stenosis. Aortic Regurgitation. Ultrasound vs. MRI. Carotid Artery Stenosis
Clinical Importance Rapid cardiovascular flow quantitation using sliceselective Fourier velocity encoding with spiral readouts Valve disease affects 10% of patients with heart disease in the U.S. Most
More informationSPM8 for Basic and Clinical Investigators. Preprocessing
SPM8 for Basic and Clinical Investigators Preprocessing fmri Preprocessing Slice timing correction Geometric distortion correction Head motion correction Temporal filtering Intensity normalization Spatial
More informationsyngo MR E11 Operator Manual Ortho Answers for life.
www.siemens.com/healthcare syngo MR E11 Operator Manual Ortho Answers for life. syngo MR E11 Operator Manual Ortho Legend Indicates a hint Is used to provide information on how to avoid operating errors
More informationCorrection for EPI Distortions Using Multi-Echo Gradient-Echo Imaging
Correction for EPI Distortions Using Multi-Echo Gradient-Echo Imaging Nan-kuei Chen and Alice M. Wyrwicz* Magnetic Resonance in Medicine 41:1206 1213 (1999) A novel and effective technique is described
More informationAccelerated MRI Techniques: Basics of Parallel Imaging and Compressed Sensing
Accelerated MRI Techniques: Basics of Parallel Imaging and Compressed Sensing Peng Hu, Ph.D. Associate Professor Department of Radiological Sciences PengHu@mednet.ucla.edu 310-267-6838 MRI... MRI has low
More informationMagnetic Resonance Angiography
Magnetic Resonance Angiography Course: Advance MRI (BIOE 594) Instructors: Dr Xiaohong Joe Zhou Dr. Shadi Othman By, Nayan Pasad Phase Contrast Angiography By Moran 1982, Bryan et. Al. 1984 and Moran et.
More informationHST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2006
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2006 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationFast Imaging Trajectories: Non-Cartesian Sampling (1)
Fast Imaging Trajectories: Non-Cartesian Sampling (1) M229 Advanced Topics in MRI Holden H. Wu, Ph.D. 2018.05.03 Department of Radiological Sciences David Geffen School of Medicine at UCLA Class Business
More informationRelease Notes. Multi-Band EPI C2P. Release HCP_v1 10 February 2014
Release Notes Multi-Band EPI C2P Release HCP_v1 10 February 2014 Installation 1. Restart the system (reboot host and MRIR) 2. Extract the.zip file to a temporary directory 3. Run the installer.bat file
More informationAn Introduction to Image Reconstruction, Processing, and their Effects in FMRI
An Introduction to Image Reconstruction, Processing, and their Effects in FMRI Daniel B. Rowe Program in Computational Sciences Department of Mathematics, Statistics, and Computer Science Marquette University
More informationMRI Image Quality Assessment
in partnership with MRI Image Quality Assessment David Collins CR-UK Cancer Imaging Centre, The Institute of Cancer Research Making the discoveries that defeat cancer Overview Current Practice Quality
More informationMB-EPI PCASL. Release Notes for Version February 2015
MB-EPI PCASL Release Notes for Version 1.0 20 February 2015 1 Background High-resolution arterial spin labeling (ASL) imaging is highly desirable in both neuroscience research and clinical applications
More informationXI Signal-to-Noise (SNR)
XI Signal-to-Noise (SNR) Lecture notes by Assaf Tal n(t) t. Noise. Characterizing Noise Noise is a random signal that gets added to all of our measurements. In D it looks like this: while in D
More informationMRI Imaging Options. Frank R. Korosec, Ph.D. Departments of Radiology and Medical Physics University of Wisconsin Madison
MRI Imaging Options Frank R. Korosec, Ph.D. Departments of Radiolog and Medical Phsics Universit of Wisconsin Madison f.korosec@hosp.wisc.edu As MR imaging becomes more developed, more imaging options
More informationImaging Notes, Part IV
BME 483 MRI Notes 34 page 1 Imaging Notes, Part IV Slice Selective Excitation The most common approach for dealing with the 3 rd (z) dimension is to use slice selective excitation. This is done by applying
More information3-D Gradient Shimming
3-D Gradient Shimming 3-D Gradient Shimming on imaging and micro-imaging systems Technical Overview Introduction Advantage statement The GE3DSHIM method is a 3-D gradient shimming procedure developed for
More informationMotion Artifacts and Suppression in MRI At a Glance
Motion Artifacts and Suppression in MRI At a Glance Xiaodong Zhong, PhD MR R&D Collaborations Siemens Healthcare MRI Motion Artifacts and Suppression At a Glance Outline Background Physics Common Motion
More informationFunctional MRI data preprocessing. Cyril Pernet, PhD
Functional MRI data preprocessing Cyril Pernet, PhD Data have been acquired, what s s next? time No matter the design, multiple volumes (made from multiple slices) have been acquired in time. Before getting
More informationSampling, Ordering, Interleaving
Sampling, Ordering, Interleaving Sampling patterns and PSFs View ordering Modulation due to transients Temporal modulations Slice interleaving Sequential, Odd/even, bit-reversed Arbitrary Other considerations:
More informationCompressed Sensing for Rapid MR Imaging
Compressed Sensing for Rapid Imaging Michael Lustig1, Juan Santos1, David Donoho2 and John Pauly1 1 Electrical Engineering Department, Stanford University 2 Statistics Department, Stanford University rapid
More informationFMRI Pre-Processing and Model- Based Statistics
FMRI Pre-Processing and Model- Based Statistics Brief intro to FMRI experiments and analysis FMRI pre-stats image processing Simple Single-Subject Statistics Multi-Level FMRI Analysis Advanced FMRI Analysis
More informationHST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008
MIT OpenCourseWare http://ocw.mit.edu HST.583 Functional Magnetic Resonance Imaging: Data Acquisition and Analysis Fall 2008 For information about citing these materials or our Terms of Use, visit: http://ocw.mit.edu/terms.
More informationTable of Contents. IntroLab < SPMLabs < Dynevor TWiki
Table of Contents Lab 1: Introduction to SPM and data checking...1 Goals of this Lab...1 Prerequisites...1 An SPM Installation...1 SPM Defaults...2 L/R Brain Orientation...2 Memory Use for Data Processing...2
More informationSources of Distortion in Functional MRI Data
Human Brain Mapping 8:80 85(1999) Sources of Distortion in Functional MRI Data Peter Jezzard* and Stuart Clare FMRIB Centre, Department of Clinical Neurology, University of Oxford, Oxford, UK Abstract:
More informationUniversity of Cape Town
Development of a 3D radial MR Imaging sequence to be used for (self) navigation during the scanning of the fetal brain in utero by Leah Morgan Thesis presented for the degree of Master of Science June
More informationQualitative Comparison of Conventional and Oblique MRI for Detection of Herniated Spinal Discs
Qualitative Comparison of Conventional and Oblique MRI for Detection of Herniated Spinal Discs Doug Dean Final Project Presentation ENGN 2500: Medical Image Analysis May 16, 2011 Outline Review of the
More informationOutline: Contrast-enhanced MRA
Outline: Contrast-enhanced MRA Background Technique Clinical Indications Future Directions Disclosures: GE Health Care: Research support Consultant: Bracco, Bayer The Basics During rapid IV infusion, Gadolinium
More informationBreast MRI Accreditation Program Clinical Image Quality Guide
Breast MRI Accreditation Program Clinical Image Quality Guide Introduction This document provides guidance on breast MRI clinical image quality and describes the criteria used by the ACR Breast MRI Accreditation
More informationRemoval of EPI Nyquist Ghost Artifacts With Two- Dimensional Phase Correction
Removal of EPI Nyquist Ghost Artifacts With Two- Dimensional Phase Correction Nan-kuei Chen 1,5 and Alice M. Wyrwicz 4 * Magnetic Resonance in Medicine 51:147 153 (004) Odd even echo inconsistencies result
More informationControlled Aliasing in Parallel Imaging Results in Higher Acceleration (CAIPIRINHA)
www.siemens.com/magnetom-world Controlled Aliasing in Parallel Imaging Results in Higher Acceleration (CAIPIRINHA) Felix Breuer; Martin Blaimer; Mark Griswold; Peter Jakob Answers for life. Controlled
More informationTOPICS 2/5/2006 8:17 PM. 2D Acquisition 3D Acquisition
TOPICS 2/5/2006 8:17 PM 2D Acquisition 3D Acquisition 2D Acquisition Involves two main steps : Slice Selection Slice selection is accomplished by spatially saturating (single or multi slice imaging) or
More informationSampling, Ordering, Interleaving
Sampling, Ordering, Interleaving Sampling patterns and PSFs View ordering Modulation due to transients Temporal modulations Timing: cine, gating, triggering Slice interleaving Sequential, Odd/even, bit-reversed
More informationAbbie M. Diak, PhD Loyola University Medical Center Dept. of Radiation Oncology
Abbie M. Diak, PhD Loyola University Medical Center Dept. of Radiation Oncology Outline High Spectral and Spatial Resolution MR Imaging (HiSS) What it is How to do it Ways to use it HiSS for Radiation
More informationAnalysis of Functional MRI Timeseries Data Using Signal Processing Techniques
Analysis of Functional MRI Timeseries Data Using Signal Processing Techniques Sea Chen Department of Biomedical Engineering Advisors: Dr. Charles A. Bouman and Dr. Mark J. Lowe S. Chen Final Exam October
More information2D spatially selective excitation pulse design and the artifact evaluation
EE 591 Project 2D spatially selective excitation pulse design and the artifact evaluation 12/08/2004 Zungho Zun Two-dimensional spatially selective excitation is used to excite a volume such as pencil
More informationBlipped-Controlled Aliasing in Parallel Imaging for Simultaneous Multislice Echo Planar Imaging With Reduced g-factor Penalty
IMAGING METHODOLOGY - Full Papers Magnetic Resonance in Medicine 67:1210 1224 (2012) Blipped-Controlled Aliasing in Parallel Imaging for Simultaneous Multislice Echo Planar Imaging With Reduced g-factor
More informationThe SIMRI project A versatile and interactive MRI simulator *
COST B21 Meeting, Lodz, 6-9 Oct. 2005 The SIMRI project A versatile and interactive MRI simulator * H. Benoit-Cattin 1, G. Collewet 2, B. Belaroussi 1, H. Saint-Jalmes 3, C. Odet 1 1 CREATIS, UMR CNRS
More informationGradient-Echo. Spin-Echo. Echo planar. Assessment of Regional Function Assessment of Global. Parallel Imaging. Function. Steady State Imaging
Gradient-Echo Spin-Echo James W. Goldfarb Ph.D. Department of Research and Education St. Francis Hospital Program in Biomedical Engineering SUNY Stony Brook Echo planar Assessment of Regional Function
More informationPartial k-space Reconstruction
Chapter 2 Partial k-space Reconstruction 2.1 Motivation for Partial k- Space Reconstruction a) Magnitude b) Phase In theory, most MRI images depict the spin density as a function of position, and hence
More informationT 1 MAPPING FOR DCE-MRI
T 1 MAPPING FOR DCE-MRI A dissertation submitted to the Faculty of Medicine, University of Malaya in partial fulfillment of the requirements for the degree of Master of Medical Physics By NURUN NAJWA BINTI
More informationImproved Spatial Localization in 3D MRSI with a Sequence Combining PSF-Choice, EPSI and a Resolution Enhancement Algorithm
Improved Spatial Localization in 3D MRSI with a Sequence Combining PSF-Choice, EPSI and a Resolution Enhancement Algorithm L.P. Panych 1,3, B. Madore 1,3, W.S. Hoge 1,3, R.V. Mulkern 2,3 1 Brigham and
More informationPartial k-space Recconstruction
Partial k-space Recconstruction John Pauly September 29, 2005 1 Motivation for Partial k-space Reconstruction a) Magnitude b) Phase In theory, most MRI images depict the spin density as a function of position,
More informationQIBA Profile: Magnetic Resonance Elastography of the Liver
5 QIBA Profile: Magnetic Resonance Elastography of the Liver Stage: A. Initial Draft July 28, 2017 10 15 20 25 30 35 40 Table of Contents Change Log:...3 Open Issues:...4 Closed Issues:...4 1. Executive
More information