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Basic Aspects of Basic Aspects of Full Field Digital Full Field Digital
MammographyMammography(FFDM)(FFDM)
FDA Approved FFDM UnitsFDA Approved FFDM Units
http://www.fda.gov/CDRH/MAMMOGRAPHY/digital.html
FFDM Units and FFDM Units and FacilitiesFacilities
http://www.acr.org/accreditation/mammography/rsna07presentation.aspx
FFDM DifferencesFFDM Differences– Image acquisition and display are separated– Wide dynamic range (versus H&D curve)– Lower Dose (~20%)
Same dose limits as for film-screen– Higher kVp (+3 kVp)– Better for dense breasts– Imaging detector can be used as AEC detector
– Automated AEC sensor adjustment (under some AEC modes)
– Use of Mo/Mo, Mo/Rh, Rh/Rh, W/Rh and W/Ag targets
FFDM DifferencesFFDM Differences
–Digital imagesRequire workstations
Post-processing image enhancement
Computer aided diagnosis
Archival issues (>9 Mbyte/image)
Good Digital Good Digital Mammo ResourceMammo Resource
© Report 05037: Comparative Specifications of Full Field Digital Mammography Systems 2005
AECAEC–Done with the image detector rather than discrete radiation detectors:
Amorphous silicon PIN diodes (with scintillator) PM tube (with scintillator) Ion chamber
–System can automatically select the densest aspect of the breast for AEC “cell” positioning or the technologist can manually select the AEC “cell” position
Prep DelayPrep Delay
Can be quite long– Up to 7 seconds– Especially in AEC mode– Very brief for film-screen mammography
Breast DoseBreast Dose
Systems display breast dose with image– Dose recorded in DICOM image header– Entrance skin exposure and/or average glandular dose
– Vendors use different dose calculation algorithms
Dance Wu & Barnes U.S. Method
Focal Spot SizeFocal Spot Size
GE Senographe 2000 D
GE Senographe
DSHologic Selenia
Siemens Mammomat Novation
Detector material
Caesium iodide /TFT
array
Caesium iodide /TFT
array
Amorphous selenium /TFT array
Amorphous selenium /TFT array
Detector type Indirect Indirect Direct Direct
Focal spot sizes (mm) .3 and .1 .3 and .1 .3 and .1 .3 and .1
Target materials Mo and Rh Mo and Rh
MoORW Mo and W
Filter materials Mo and Rh Mo and Rh
Mo and RhOR
Rh and Ag Mo and Rh
© Report 05037: Comparative Specifications of Full Field Digital Mammography Systems 2005
Fuji Digital Fuji Digital MammographyMammography
ClearView-CSM Reads image plate from both sides
50 micron resolution 10 lp/mm
FFDM DetectorsFFDM Detectors
Scintillating phosphor (CsI columns) on an array of amorphous silicon photodiodes using thin-film transistor (TFT) flat panel technology (GE)– ~100 micron pixels– Mo/Mo. Mo/Rh, Rh/Rh
Amorphous selenium (direct conversion) using (TFT) flat panel technology (Siemens, Hologic)– ~70 micron pixels – Mo/Mo, Mo/Rh OR W/Rh, W/Ag for Hologic– Mo/Mo, Mo/Rh, W/Rh for Siemens
Computed radiography (Fuji)– ~50 micron pixels
Slot scanning CCD (Fischer? Fischer Medical Technologies?)– ~27 micron pixels
Digital Mammography: X-ray SourceDigital Mammography: X-ray Source
Target Material and Characteristic X-ray Emission• Mo (kα=17.4 keV; kβ =19.6 keV)• Rh (kα=20.2 keV; kβ =22.7 keV)• W (kα=58.6 keV; kβ =67.4 keV)
Filter Material and K-edge (Absorption Edge)• Mo (K edge = 20.0 keV)• Rh (K edge = 23.3 keV)• Ag (K edge = 25.5 keV)
X-ray spectral distribution is determined by:– anode target material–filter material and thickness
–kVp. Screen-film mammography emphasizes characteristic X-rays rather than Bremmstrahlung photons.
Spectra of Mo/Mo and Mo/Rh at 28 kVp
Slide courtesy of Hologic
©1994 Williams & Wilkins
Mo & Rhtargets
Mo/Rh
©1994 Williams & Wilkins
Mo/Mo
Rh/Rh
Spectra of W/Rh and W/Ag at 28 kVp
Slide courtesy of Hologic
X-Ray SpectraX-Ray Spectra
Focal Spot SizeFocal Spot Size
GE Senographe
2000 DGE Senographe
DSHologic Selenia
Siemens Mammomat Novation
Grid technology Linear Linear Cellular (HTC) Linear
Grid interspcae filler Paper Paper Air Paper
Maximum field size (cm) 19 x 23 19 x 23 24 x 29 23 x 29
Maximum image matrix (pixels) 1914 x 2294 1914 x 2294 3328 x 4096 3328 x 4096
Pixel pitch (microns) 100 100 70 70
Hich contrast limiting resolution (lp/mm) 5 5 > 7 > 7
© Report 05037: Comparative Specifications of Full Field Digital Mammography Systems 2005
©1994 Williams & Wilkins
System MTF
Scattered Radiation Scattered Radiation ControlControl
Only 40-75% of the possible contrast is imaged in mammography unless scatter is controlled.
Scattered Radiation Scattered Radiation ControlControlLinear Grids
–Grids preferentially remove scattered photons.
–Lead laminae separated by radiolucent spacers.
–Grid ratio (height of lamina/distance between laminae): 4:1 or 5:1 w/ 30-40 lines/cm.
–Conventional grids are 8:1 to 12:1 (up to 43 lines/cm).
Scattered Radiation Scattered Radiation ControlControl
Linear Grids –Grids move (linearly or oscillatory L<-->R) during an exposure (20 or more grid line spacings) to blur out grid lines.
–Short exposures can cause gridline artifacts that result from insufficient motion.
–Mammography grids transmit 60-70% of primary X-rays and absorb 75-85% of the scattered X-rays.
Scattered Radiation Scattered Radiation ControlControl
Linear Grids –Breast dose is increased by grids (Bucky Factor: x2 to x3) w/40% improvement in contrast.
–Laminae are focused to the focal spot to prevent grid cut off.
High Transmission Cellular (HTC) Grids– Focused– Increased 2D absorption of scattered radiation
– Increase contrast– Must move the grid a very precise distance during exposure regardless of exposure duration
– Essentially same grid ratio and dose as conventional linear grids
Scattered Radiation Scattered Radiation ControlControl
HTC GridHTC Grid
http://www.hologic.com/oem/pdf/W-BI-HTC_HTC%20GRID_09-04.pdf
HTC GridHTC Grid
http://www.hologic.com/oem/pdf/W-BI-HTC_HTC%20GRID_09-04.pdf
HTC GridHTC Grid
http://www.hologic.com/oem/pdf/W-BI-HTC_HTC%20GRID_09-04.pdf
HTC GridHTC Grid
http://www.hologic.com/oem/pdf/W-BI-HTC_HTC%20GRID_09-04.pdf
Focal Spot SizeFocal Spot Size
GE Senographe
2000 DGE Senographe
DSHologic Selenia
Siemens Mammomat Novation
Acquisition bit depth (bits) 14 14 14 14
Image bit depth (bits) 8 8 14 14
Workstation bit depth 10 10 12 10
Maximum image size (Mbyte) 9 9 27 27Time to display image on acquisition workstation (s) 10 <15 10 to 15 40 to 50
Reject analysis No Yes Yes Yes
Stereotactic biopsy devices Yes Yes
© Report 05037: Comparative Specifications of Full Field Digital Mammography Systems 2005
Future of Digital Future of Digital MammographyMammography(as of 2005)(as of 2005)
GE Medical Systems: – tomosynthesis.
Hologic:– tomosynthesis – dual energy imaging – imaging with contrast media.
Siemens Medical Solutions: – tomosynthesis– increased post processing capabilities at the review workstation
– improved reporting workstation with image fusion (ultrasound, MRI, etc)
– 2nd generation CAD.
© Report 05037: Comparative Specifications of Full Field Digital Mammography Systems 2005
TomosynthesisTomosynthesis
http://www.hologic.com/wh/tomomov.cfm
3:00 -7:00
Breast Tomosynthesis Breast Tomosynthesis (Hologic)(Hologic)
Data acquisition– 15 discrete views– Limited arc (~50 degrees?)– 7 frames/sec– 5 second exposure
Reconstruction– 50 slices– 1 mm thick– Back projection
TomosynthesisTomosynthesis
Breast CTBreast CT
U C Davis
Breast CTBreast CT
U C Davis
Cone Beam Breast CTCone Beam Breast CT
University of Rochester
300 views 10 seconds
Cone Beam Breast CTCone Beam Breast CT
University of Rochester
Cone Beam Breast CTCone Beam Breast CT
http://www.urmc.rochester.edu/pr/current_research/Cone_Beam/video.cfm
ReferencesReferences– ©NCRP 2006
NCRP Report 149, “A Guide to Mammography and Other Breast Imaging Procedures” National Council on Radiation Protection and Measurements, 2004
– ©1994 Williams & Wilkins Bushberg, JT, Seibert, JA, Leidholdt, EM Jr., Boone, JM, ”The Essential Physics of Medical Imaging” Williams & Wilkins, Baltimore, Maryland, 1994
– ©1993 RSNA Haus, AG, Yaffe, MJ, Eds., “Syllabus: A Categorical Course in Physics Technical Aspects of Breast Imaging”, 2nd Edition, RSNA, 1993
– ©1992 RSNA Haus, AG, Yaffe, MJ, Eds., “Syllabus: A Categorical Course in Physics Technical Aspects of Breast Imaging”, RSNA, 1992
– ©1987 IOP Publishing Johns, PC, Yaffe, MJ, “X-Ray characterisation 675-695 of normal and neoplastic breast tissues”, Phys Med Biol, 1987, 32,