WO2006071922A2 - Combined pet/mr imaging system and apd-bassed pet detector for use in simultaneous pet/mr imaging - Google Patents
Combined pet/mr imaging system and apd-bassed pet detector for use in simultaneous pet/mr imaging Download PDFInfo
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- WO2006071922A2 WO2006071922A2 PCT/US2005/047196 US2005047196W WO2006071922A2 WO 2006071922 A2 WO2006071922 A2 WO 2006071922A2 US 2005047196 W US2005047196 W US 2005047196W WO 2006071922 A2 WO2006071922 A2 WO 2006071922A2
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/44—Arrangements or instruments for measuring magnetic variables involving magnetic resonance using nuclear magnetic resonance [NMR]
- G01R33/48—NMR imaging systems
- G01R33/4808—Multimodal MR, e.g. MR combined with positron emission tomography [PET], MR combined with ultrasound or MR combined with computed tomography [CT]
- G01R33/481—MR combined with positron emission tomography [PET] or single photon emission computed tomography [SPECT]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves
- A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computerised tomographs
- A61B6/037—Emission tomography
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/24—Arrangements or instruments for measuring magnetic variables involving magnetic resonance for measuring direction or magnitude of magnetic fields or magnetic flux
- G01R33/26—Arrangements or instruments for measuring magnetic variables involving magnetic resonance for measuring direction or magnitude of magnetic fields or magnetic flux using optical pumping
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/30—Sample handling arrangements, e.g. sample cells, spinning mechanisms
- G01R33/307—Sample handling arrangements, e.g. sample cells, spinning mechanisms specially adapted for moving the sample relative to the MR system, e.g. spinning mechanisms, flow cells or means for positioning the sample inside a spectrometer
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01R—MEASURING ELECTRIC VARIABLES; MEASURING MAGNETIC VARIABLES
- G01R33/00—Arrangements or instruments for measuring magnetic variables
- G01R33/20—Arrangements or instruments for measuring magnetic variables involving magnetic resonance
- G01R33/28—Details of apparatus provided for in groups G01R33/44 - G01R33/64
- G01R33/38—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field
- G01R33/381—Systems for generation, homogenisation or stabilisation of the main or gradient magnetic field using electromagnets
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/1603—Measuring radiation intensity with a combination of at least two different types of detector
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/2018—Scintillation-photodiode combinations
- G01T1/20182—Modular detectors, e.g. tiled scintillators or tiled photodiodes
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/2018—Scintillation-photodiode combinations
- G01T1/20185—Coupling means between the photodiode and the scintillator, e.g. optical couplings using adhesives with wavelength-shifting fibres
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/2018—Scintillation-photodiode combinations
- G01T1/20188—Auxiliary details, e.g. casings or cooling
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01V—GEOPHYSICS; GRAVITATIONAL MEASUREMENTS; DETECTING MASSES OR OBJECTS; TAGS
- G01V3/00—Electric or magnetic prospecting or detecting; Measuring magnetic field characteristics of the earth, e.g. declination, deviation
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
- A61B8/5238—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
- A61B8/5261—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image combining images from different diagnostic modalities, e.g. ultrasound and X-ray
Definitions
- the present invention generally relates to the field of medical imaging, and systems for obtaining diagnostic images such as nuclear medicine images and magnetic resonance (MR) images.
- diagnostic images such as nuclear medicine images and magnetic resonance (MR) images.
- the present invention relates to multiple modality imaging systems and methods for obtaining diagnostic images of multiple modalities, such as nuclear medicine images from positron emission tomography (PET) data and magnetic resonance imaging (MRI) data.
- PET images and MR images can be obtained either sequentially or simultaneously.
- Nuclear medicine is a unique medical specialty wherein radiation is used to acquire images which show the function and anatomy of organs, bones or tissues of the body.
- Radiopharmaceuticals are introduced into the body, either by injection or ingestion, and are attracted to specific organs, bones or tissues of interest.
- Such radiopharmaceuticals produce gamma photon emissions which emanate from the body and are captured by a scintillation crystal, with which the photons interact to produce flashes of light or "events.”
- Events are detected by an array of photodetectors, such as photomultiplier tubes, and their spatial locations or positions are calculated and stored. In this way, an image of the organ or tissue under study is created from detection of the distribution of the radioisotopes in the body.
- PET Positron Emission Tomography
- PET is used to produce images for diagnosing the biochemistry or physiology of a specific organ, tumor or other metabolically active site.
- Measurement of the tissue concentration of a positron emitting radionuclide is based on coincidence detection of the two gamma photons arising from positron annihilation.
- two 511 keV gamma photons are simultaneously produced and travel in approximately opposite directions.
- Gamma photons produced by an annihilation event can be detected by a pair of oppositely disposed radiation detectors capable of producing a signal in response to the interaction of the gamma photons with a scintillation crystal.
- Annihilation events are typically identified by a time coincidence between the detection of the two 511 keV gamma photons in the two oppositely disposed detectors, Le 1 , the gamma photon emissions are detected virtually simultaneously by each detector.
- two oppositely disposed gamma photons each strike an oppositely disposed detector to produce a time coincidence event, they also identify a line of response, or LOR, along which the annihilation event has occurred.
- PET is described in U.S. Patent No. 6,858,847, which patent is incorporated herein by reference in its entirety.
- the LORs defined by the coincidence events are used to reconstruct a three- dimensional distribution of the positron-emitting radionuclide within the patient.
- PET is particularly useful in obtaining images that reveal bioprocesses, e ⁇ the functioning of bodily organs such as the heart, brain, lungs, etc. and bodily tissues and structures such as the circulatory system.
- Magnetic Resonance Imaging is primarily used for obtaining high quality, high resolution anatomical and structural images of the body.
- MRI Magnetic Resonance Imaging
- the major components of an MRI imager include a cylindrical magnet, gradient coils within the magnet, an RF coil within the gradient coil, and an RF shield that prevents the high power RF pulses from radiating outside of the MR imager, and keeps extraneous RF signals from being detected by the imager.
- a patient is placed on a patient bed or table within the magnet and is surrounded by the gradient and RF coils.
- the magnet produces a B 0 magnetic field for the imaging procedure.
- the gradient coils produce a gradient in the B 0 field in the X, Y, and Z directions.
- the RF coil produces a B 1 magnetic field necessary to rotate the spins of the nuclei by 90° or 180°.
- the RF coil also detects the nuclear magnetic resonance signal from the spins within the body.
- a radio frequency source produces a sine wave of the desired frequency.
- the present invention overcomes the problems in the prior art, by providing an APD-based (Avalanche PhotoDiode) PET detector with a MR scanner. Because APDs are quite small and are magnetically insensitive, a detector could be designed that could fit into the tunnel of the MR scanner either as a removable insert for head and extremity imaging, or could be fully integrated into the MR scanner itself.
- APD-based PET detector Avalanche PhotoDiode
- FIG. 1 is a diagram of a PET detector ring in accordance with an embodiment of the invention
- FIG. 2 is a circuit block diagram of the components of a detector module as incorporated in FIG. 1;
- FIG. 3 is a perspective view of a combined PET/MR system in accordance with an embodiment of the invention, showing a plurality of PET detector rings within an MR field of view;
- FIG. 4 is a perspective view of a combined PET/MR system in accordance with another embodiment of the invention, showing a plurality of planar PET detector panels positioned on the end of a MR scanner;
- FIG. 5 is a perspective view of a PET detector module in accordance with another embodiment of the invention.
- FIG. 6 is a position profile of a readout of the detector as shown in FIG. 5;
- FIG. 7 is a composite diagram showing 22 Na energy spectra and position profile of one block in a PET detector module in accordance with the invention, with the MR RF sequence on;
- FIG. 8 shows respective MR, PET and fused PET/MR images of a Derenzo phantom acquired in accordance with a combined PET/MR system of the present invention.
- FIG. 9 is a perspective diagram of stacked-board APD detector design in accordance with the invention, to fit in the tunnel of an MR scanner for brain imaging.
- a PET scanner in accordance with one embodiment of the invention includes a plurality of detector modules arranged in a ring configuration.
- each detector module includes a scintillator block that is optically coupled through a light guide to a solid state photodetector or array of photodetectors, such as avalanche photodiodes (APDs) or other semiconductor-based type of photodetector.
- APDs avalanche photodiodes
- Each individual solid-state photodetector may be optically coupled to more than one scintillator, or may be coupled in a one-to-one scintillator to photodetector arrangement.
- Each APD is electrically connected to a high voltage source. Multiple APDs may share a single voltage source.
- the charge created in the APDs is collected in a preamplifier, such as a charge- sensitive preamplifier, transimpedance preamplifier or voltage-sensitive preamplifier.
- the pulse signals produced by the preamplifiers are then inputted to appropriate pulse processing electronics, as generally known in the art.
- Fig. 3 illustrates one possible embodiment of the invention wherein a plurality of PET detector rings, such as 3, are disposed within an MRI magnet. Accordingly, each detector ring has an outer diameter dimensioned to be received within the geometry of the MRI scanner.
- the number of PET detector rings may more than 3 or less than 3, and in a particular alternate embodiment a single PET detector ring may be provided.
- a patient table or bed is provided to receive a patient to be imaged. PET and MR data acquisitions are carried out on the patient, either simultaneously, in an interlaced or interleaved manner, or sequentially.
- FIG. 4 An additional alternate embodiment of the invention is shown in Fig. 4, wherein two planar PET detector panels are provided and positioned 180° apart within the MR scanner FOV.
- the PET detector panels also may be positioned at the end of the MR patient gantry outside the FOV. While two panels are shown in the example embodiment of Fig. 4, it will be recognized that more than two detector panels may be provided in various alternative configurations.
- the detector panels may be configured to rotate about the patient, either partially or a full 360°.
- the detector panels also may be configured to be stationary.
- the PET detector modules can be either permanently mounted within or on the MRI scanner, or be retractable therefrom.
- An APD-based PET module has been built and tested for use in a MR scanner for simultaneous PET/MR imaging according to the present invention.
- the module consisted of 4 optically isolated scintillator blocks each read out by a 2 x 2 APD array, as shown in Fig. 5.
- One basic APD detector design according to an embodiment of the invention is based on an LSO block design.
- the scintillator blocks are 8 x 8 arrays of 2 mm x 2 mm x 20 mm LSO crystals coupled to glass light guides.
- the APDs are coupled to the glass light guides.
- the APDs can be any commercially available APD, such as, e.g., Hamamatsu S8664-55 APDs in a custom package, or APDs available from Perkin-Elmer.
- the APD signals are amplified by a charge-sensitive preamplifier ASIC, and shaped by a pole-zero circuit. Therefore one module contained 4 LSO blocks, 16 APDs, 2 ASIC preamplifiers, and 16 channels of pole-zero electronics.
- the outputs of the modules were sampled and digitized by Siemens Pico3D electronics, which determine energy, timing and position.
- a typical position profile is shown in Fig. 6.
- the average crystal time resolution (against a plastic scintillator on a PMT) was 1.8 ns, while the average crystal energy resolution was 17%.
- Each module was packaged in a box made of copper-coated FR-4 board.
- the FR-4 board had a lO ⁇ m (1/8 oz.) thick copper coating for RF shielding.
- the output signal cables were 7 m long, twisted-pair cables with an RJ45 connector. All of the cables were connected to a feed- through plate mounted to the wall in the RF-shielded MR room.
- the power supplies and Pico3D electronics were in a technical room on the other side of the feed-through plate. This ensured that the MR electronics were shielded from the PET electronics and vice versa.
- the modules were mounted on a RF shielded gantry that was positioned inside the tunnel of a Siemens Symphony 1.5 Tesla MR scanner. A transmit/receive head coil was placed in the center of the gantry.
- a 22Na source was used for setup and compatibility measurements.
- a small Derenzo phantom 32 mm diameter and 16 mm tall
- the phantom could be rotated in 19 steps for 180° rotation to allow 3D imaging.
- the phantom was filled with water and 1.25 g NiSO4 / liter (as an MR contrast agent) and about 50 MBq FDG.
- Measurements were performed to determine the effects the PET modules had on the MR performance as well as the effect the magnetic field, RF and gradient pulses had on the PET performance. While the PET modules were acquiring data; MR sequences were being performed to quantify the effect the PET modules had on the MR image. Baseline MR images were acquired with the PET modules in and out of the MR scanner. When the PET modules were inside the MR tunnel, the signal-to-noise ratio of the MR decreased by 15%. Thus, this effect could be reduced by using improved shielding of the PET modules and cables.
- Spikes are RF signals with a broadband RF spectrum generated, e ⁇ , by electrostatic discharges. Spikes can produce a high background noise level or a sine wave artifact in the image. No spikes were observed in the MR baseline image. An MR head phantom image was acquired with the PET modules in place. Any magnetic components close to the phantom would introduce distortion artifacts in the phantom image. No interference was seen due to the PET modules or gantry, as all of the components are non-magnetic or far enough away from the phantom to eliminate any significant interference.
- the MR scanner transmitted varying degrees of gradient and RF pulse sequences.
- the APD output signals and CFD trigger were observed on an oscilloscope to see the effects.
- Position profile and energy spectra data were also acquired during gradient and RF pulse sequencing.
- Static magnetic field measurements were performed to determine the effects the PET modules had on the MR performance as well as the effect that the magnetic field, RF and gradient pulses had on the PET performance. There was no observable effect from the static magnetic field of the MR scanner.
- a gradient sequence was set to 20 mT/m with a ramp time of 0.1 ms and a 2 ms repetition time.
- the gradient pulses were bipolar with no top and were transmitted in all 3 directions. This is a very aggressive sequence with respect to generating as much induction as possible by the MR scanner. This sequence was transmitted for 20 minutes.
- the detector was placed in the region of maximum flux density.
- the gradient pulses were observed in the output signals from the detector modules using an oscilloscope. But the gradient pulses did not trigger the CFD and therefore were not seen in the energy spectra and position profile. However, the gradient pulses did block the true event signals, effectively increasing the dead time of the system. This effect could be reduced by minimizing ground loops within the PET system.
- a RF sequence was transmitted with an amplitude of 730 V, a pulse width of 1 ms and a repetition time of 10 ms. This corresponds to a Bl flux density of about 30 ⁇ T. Again, this is an aggressive sequence for the MR scanner. This sequence was transmitted for 10 minutes.
- the RF pulses were observed in the output signals from the detector modules using an oscilloscope. But unlike the gradient pulses, the RF pulses did trigger the CFD and therefore were seen in the energy spectra. However, the RF pulses created low energy counts in the energy spectra and therefore did not affect the 511 keV photopeak. Due to the normal system energy gating of the PET electronics, the effect of the RF pulses was not seen in the position profile as shown in Fig. 7. But the RF pulses would also increase the dead time of the PET system. Better RF shielding could help reduce this effect.
- PET and MR images were acquired simultaneously to show proof-of-principle compatibility for an integrated system.
- the PET image was acquired using a step-and-shoot method.
- PET data were acquired with the Derenzo phantom for each of 19 rotational positions.
- the PET acquisition time ranged from 6 min. for the first step to 21 min. for the last step (in order to correct for the FDG half-life).
- an MR image was acquired using a spin echo sequence followed by a 2D gradient-echo sequence and a 3D gradient echo sequence for a total acquisition time of 5 min.
- the PET image was reconstructed using all of the positions.
- MR, PET and fused images are shown in Fig. 8.
- the images show no artifacts. AU of the holes can be clearly seen in the MR image and the smallest holes visible in the PET image are the 2 mm holes.
- These measurements demonstrate the benefits of an integrated APD-based PET/MR scanner in accordance with the invention. Simultaneous PET and MR imaging is achievable without any image artifacts or distortion.
- An alternate modular APD detector for a PET/MR brain scanner can be based on a stacked board design in order to fit into the tight space constraints of the MR tunnel, as shown in Fig. 9.
Abstract
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Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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CA 2592685 CA2592685C (en) | 2004-12-29 | 2005-12-29 | Combined pet/mr imaging system and apd-based pet detector for use in simultaneous pet/mr imaging |
EP05855710A EP1853161A4 (en) | 2004-12-29 | 2005-12-29 | Combined pet/mr imaging system and apd-based pet detector for use in simultaneous pet/mr imaging |
JP2007549575A JP2008525161A (en) | 2004-12-29 | 2005-12-29 | Positron emission tomography-magnetic resonance tomography combined imaging system and positron emission tomography-avalanche photodiode based positron emission tomography detector used for simultaneous imaging of magnetic resonance tomography |
AU2005322793A AU2005322793B8 (en) | 2004-12-29 | 2005-12-29 | Combined PET/MR imaging system and APD-based PET detector for use in simultaneous PET/MR imaging |
Applications Claiming Priority (4)
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US64007304P | 2004-12-29 | 2004-12-29 | |
US60/640,073 | 2004-12-29 | ||
US73899805P | 2005-11-23 | 2005-11-23 | |
US60/738,998 | 2005-11-23 |
Publications (2)
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WO2006071922A2 true WO2006071922A2 (en) | 2006-07-06 |
WO2006071922A3 WO2006071922A3 (en) | 2007-05-31 |
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PCT/US2005/047196 WO2006071922A2 (en) | 2004-12-29 | 2005-12-29 | Combined pet/mr imaging system and apd-bassed pet detector for use in simultaneous pet/mr imaging |
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US (2) | US9121893B2 (en) |
EP (1) | EP1853161A4 (en) |
JP (2) | JP2008525161A (en) |
KR (1) | KR100914429B1 (en) |
AU (1) | AU2005322793B8 (en) |
CA (1) | CA2592685C (en) |
WO (1) | WO2006071922A2 (en) |
Cited By (31)
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DE102006036572A1 (en) * | 2006-08-04 | 2008-02-14 | Siemens Ag | Device for superimposed MRI and PET imaging |
JP2008155026A (en) * | 2006-12-22 | 2008-07-10 | Siemens Ag | Method for activating hybrid medical imaging unit and hybrid medical imaging unit |
JP2008155025A (en) * | 2006-12-22 | 2008-07-10 | Siemens Ag | Method for activating hybrid medical imaging unit and hybrid medical imaging unit |
WO2008127369A2 (en) | 2006-10-31 | 2008-10-23 | Koninklijke Philips Electronics N. V. | Hybrid pet/mr imaging systems |
DE102007037102A1 (en) | 2007-08-07 | 2009-02-26 | Siemens Ag | Combined MR / PET device on a mobile basis |
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US7667457B2 (en) | 2006-12-22 | 2010-02-23 | General Electric Co. | System and apparatus for detecting gamma rays in a PET/MRI scanner |
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JP2010525857A (en) * | 2007-05-04 | 2010-07-29 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Hybrid MR / PET with correction of MR coil absorption |
EP2241905A2 (en) | 2009-02-24 | 2010-10-20 | Sungkyunkwan University Foundation for Corporate Collaboration | PET-MRI combination apparatus |
JP2011514518A (en) * | 2008-02-25 | 2011-05-06 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Conformal backbone for radiation detectors |
KR101047662B1 (en) * | 2008-11-27 | 2011-07-07 | 성균관대학교산학협력단 | PET-MRI Convergence System |
US8013607B2 (en) | 2006-10-31 | 2011-09-06 | Koninklijke Philips Electronics N.V. | Magnetic shielding for a PET detector system |
JP2011527669A (en) * | 2008-07-09 | 2011-11-04 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | Physiological pharmacokinetic analysis for complex molecular MRI and dynamic PET imaging |
US20110288401A1 (en) * | 2009-02-17 | 2011-11-24 | Koninklijke Philips Electronics N.V. | Big bore pet/mr system |
US8073527B2 (en) | 2006-09-29 | 2011-12-06 | Siemens Aktiengesellschaft | Field generating unit of a combined MR/PET system |
EP2369358A3 (en) * | 2010-03-09 | 2012-01-04 | National Institute of Radiological Sciences | PET/MRI device, pet device, and image reconstruction system |
US8188736B2 (en) | 2007-01-11 | 2012-05-29 | Koninklijke Philips Electronics N.V. | PET/MR scanners for simultaneous PET and MR imaging |
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AU2005322793B8 (en) | 2010-03-25 |
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US20150369890A1 (en) | 2015-12-24 |
US9121893B2 (en) | 2015-09-01 |
KR100914429B1 (en) | 2009-08-28 |
CA2592685C (en) | 2011-11-08 |
AU2005322793B2 (en) | 2009-11-26 |
US10036790B2 (en) | 2018-07-31 |
US20070102641A1 (en) | 2007-05-10 |
EP1853161A4 (en) | 2011-03-23 |
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