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WO1998016852A1 - Petite camera pivotante de tomographie - Google Patents

Petite camera pivotante de tomographie Download PDF

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Publication number
WO1998016852A1
WO1998016852A1 PCT/US1997/017224 US9717224W WO9816852A1 WO 1998016852 A1 WO1998016852 A1 WO 1998016852A1 US 9717224 W US9717224 W US 9717224W WO 9816852 A1 WO9816852 A1 WO 9816852A1
Authority
WO
WIPO (PCT)
Prior art keywords
semiconductor
gamma
radiation
radiation detector
gamma camera
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US1997/017224
Other languages
English (en)
Inventor
Raymond P. Devito
Guenter Schwierz
Peggy C. Hawman
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Siemens Medical Solutions USA Inc
Original Assignee
Siemens Medical Systems Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Siemens Medical Systems Inc filed Critical Siemens Medical Systems Inc
Publication of WO1998016852A1 publication Critical patent/WO1998016852A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • 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
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/037—Emission tomography

Definitions

  • This disclosure relates to Single Photon Emission Computed Tomography (SPECT) , and in particular to a rotating camera for use in SPECT applications.
  • SPECT Single Photon Emission Computed Tomography
  • SPECT belongs to a group of tomographic imaging techniques which compute three dimensional (3-D) images of an object from a set of projection images.
  • SPECT a gamma camera having a detector with an imaging window or detection region collects a plurality of projection data from a plurality of projection directions.
  • 3-D three dimensional
  • a gamma camera having a detector with an imaging window or detection region collects a plurality of projection data from a plurality of projection directions.
  • limited angle tomography an incomplete range of projections are utilized, and so such techniques suffer from distortions associated with insufficient data stemming from the incomplete range.
  • Ectomography is one reconstruction method that attempts to compensate for incomplete projection data and to produce 3-D images from the incomplete projection data.
  • slant hole collimators are typically employed with detectors having a large field of view, in which a slant angle of the slant hole collimator can be increased to reduce the level of distortion.
  • increasing the slant angle of the collimator decreases the size of the reconstruction volume, so there is a trade-off between the level of distortion and the size of the reconstruction volume.
  • Conventional SPECT systems employ large (approximately 300 square inch) detectors mounted on a stationary gantry. This gantry facilitates the motion of the system so that the detector is able to travel a path that can orbit the patient.
  • Limited angle tomographic devices normally do not orbit the patient but rather view the object mostly from one direction. For example, as shown in FIG.
  • a gamma camera detector 10 in the prior art is positioned to view the object of interest 16 (such as a heart) in the patient 18 with slant collimation employed on the detector 14. Additional support , structure (not shown in FIG. 1) is provided to rotate the detector around the support axis 12.
  • the camera 10 in the prior art typically has the collimator 14 which receives and colli ates radiation, which is passed through a crystal 20, such as an Nal crystal.
  • the incident gamma ray is converted to a scintillation flash, and then passes through a light pipe 22 for amplification by at least one photomultiplier tube (PMT) 24, which generates corresponding signals.
  • the signals are then processed by a pre-amplifier circuit 26 to generate corresponding scintillation detection signals for subsequent processing and imaging.
  • PMT photomultiplier tube
  • SPECT systems Due to such relatively large dimensions of the camera 10 and supporting structure, such SPECT systems must be engineered with adequate and often voluminous supporting structure in a facility such as a hospital. A need exists for a generally small and/or compact SPECT system, to economize on space in a facility.
  • the patient must be brought to the SPECT system for imaging. Since the patient may be immobile or restricted to an intensive care unit or may experience complications from transport to the SPECT system, such as stroke victims, the use of such large and stationary SPECT systems for diagnosis of the patient may also be detrimental to the patient.
  • the large size of the detector and supporting structure previous SPECT systems have not been able to be mobile.
  • detectors having an imaging window or detection region oriented in one general direction such limited angle tomography techniques typically have the detector fixed in the single direction relative to the axis of rotation of the detector, thus limiting the angular range of the detectQr.
  • a gamma camera which has a semiconductor- based radiation detector which responds to reference Fig. 2 gamma radiation from a target for generating corresponding detection signals for use in tomographic imaging of the target.
  • the semiconductor-based radiation detector is mounted in a mobile support structure to facilitate transport of the gamma camera.
  • An armature mounts the semiconductor-based radiation detector to the mobile support structure, and the armature is orientable in a plurality of positions for positioning the semiconductor- based radiation detector in a plurality of orientations about the target.
  • a rotatable mounting device having a central axis may be included for rotatably mounting the semiconductor-based radiation detector to the armature, to allow the semiconductor-based radiation detector to be oriented in a plurality of tilt angles with respect to a plane.
  • a slant angle collimator is used to provide an angular window for reception of the gamma radiation.
  • a parallel-hole collimator is used to provide a window for reception of the gamma radiation.
  • At least one armature is provided which is rotatable about an axis, and at least one semiconductor-based radiation detector is operatively connected to a corresponding armature and responds to rotation thereof for orbiting about the target and detecting gamma radiation therefrom.
  • the detectors may be readily rotated about a portion of the target.
  • the detectors may be rotated about any arbitrary axis, such as an axis passing through the target.
  • the compact size of the detectors also allow the detectors to be positioned relatively near the target and rotatable about an axis and directed to the target. Accordingly, multiple detectors may be focused on the target for improved imaging.
  • Imaging samples of, for example, the heart may be obtained from a variety of angles, with the angles set to be either large or small.
  • the variable tilt angles allow for smaller viewing angles to be employed by the detectors and/or the collimators, with reduced distortion to provide improved accuracy in the data gathering by the detectors.
  • the ability to tilt and to rotate the detectors about an axis and directed toward a target provides the disclosed gamma camera with the ability to cover the same or more directional aspects of the target than prior art devices. The amount and quality of the imaging data is thus improved.
  • FIG. 1 is a schematic drawing of limited angle SPECT system in the prior art
  • FIG. 2 is a schematic drawing of the disclosed SPECT system in comparison with the prior art SPECT system of FIG. 1;
  • FIG. 3 is a schematic drawing of the disclosed SPECT camera system in use with a patient;
  • FIG. 4 is a schematic drawing of a multiple camera SPECT system in use with a patient;
  • FIG. 5 is a schematic drawing of an alternative embodiment of the »pair of cameras of FIG. 4 with the detectors tilted;
  • FIG. 6 is a schematic drawing of an alternative embodiment of the pair of cameras of FIG. 4 with the detectors tilted to substantially face each other for SPECT applications with full projection capability.
  • the present disclosure describes a SPECT gamma camera 28 illustrated with relative dimensions in comparison with the gamma camera 10 of the prior art.
  • the disclosed gamma camera 28 has relatively smaller dimensions than the gamma camera 10 of the prior art, in which the disclosed SPECT gamma camera system of FIG. 3 has improved imaging capabilities and may be configured for mobile applications.
  • the disclosed camera In the illustrative embodiment, the disclosed camera
  • the disclosed camera 28 has a collimator 30 for collimating radiation, and for applying the collimated radiation to a semiconductor-based radiation detector 32.
  • semiconductor-based radiation detectors 32 are known in the art, as described in G.F. Knoll, "Radiation Detection and Measurement, Second Edition", John Wiley & Sons: New York, pp. 465-469.
  • the disclosed camera 28 has the semiconductor-based radiation detector 32 composed of cadmium telluride (CdTe) or cadmium zinc telluride (CZT or CdZiTe) which are from 1 mm to over 1 cm in diameter, with such semiconductor-based detectors being rugged and stable in field use, and operable routinely at temperatures up to 30° C without excessive thermal noise.
  • CdTe cadmium telluride
  • CZT or CdZiTe cadmium zinc telluride
  • the disclosed camera 28 may be portable, and is well-suited for field use; i.e. for transport to diverse environments, incl ⁇ ding relatively warm environments without thermal noise impairing the functioning of the detector 32.
  • the height of the radiation detector 32 in conjunction with the collimator 30 may be reduced to have an overall height of about 1 inch, to provide a more compact configuration.
  • the radiation detector 32 Upon receiving the gamma radiation from the collimator 30, the radiation detector 32 generates corresponding signals which are processed by a pre-amplifier circuit 34 to generate corresponding detection signals for subsequent processing and imaging.
  • the pre-amplifier circuit 34 may be an application specific integrated circuit (ASIC) which permits the pre-amplifier circuit 34 to have relatively small dimensions as well. Accordingly, the overall camera 28, having the collimator 30, the radiation detector 32, and the pre-amplifier circuit 34, may be constructed to be not only compact and small but also lightweight, relative to detectors in the prior art such as camera 10.
  • the camera 28 may be mounted on a relatively lightweight arm 36 using a mounting device 38.
  • the arm 36 may be composed of aluminum and/or other lightweight materials, and thereupon connected to additional support structure (not shown in FIGS. 2-3) which may include mechanisms for mobility such as wheels, casters, and/or handles for pushing, pulling, carrying, or otherwise transporting the camera 28 and associated support structure to a patient.
  • the compact and lightweight construction of the camera 28 also facilitates the ability of the support structure and arm 36 to rotate the camera 28 for SPECT applications.
  • such compactness and lightweight construction also provide ' advantages in control of the orientation and rotation of the camera 28.
  • the camera 28 would provide less torque on the support structure than the camera 10 in the prior art, and so may be controlled by servomechanisms with less deviation in the distance from the target 16 during operation.
  • more sensitive servomechanisms may be used to provide increased accuracy in the control of the camera 28.
  • rotation speeds may be increased without wear and tear on the support structure to provide a greater number of samples per unit of time.
  • a single tomographic camera 28 having a slant angle collimator 30 may be used to receive radiation from the target; i.e. the heart 16.
  • multiple cameras 28 may be used.
  • a plurality 40, 42 of the disclosed SPECT gamma cameras 28 of FIG. 2 are used, which are mounted upon a common armature 44.
  • the heart 16 is imaged from radiation along overlapping projections to the plurality 40, 42 of cameras.
  • a pair of cameras are employed.
  • the disclosed camera 28 of FIG. 2 may be of relatively compact and lightweight construction, it is contemplated that more that two cameras may be used, which may be mounted in various configurations on one or more armatures and support structures. For example, as shown in FIG.
  • the cameras 40, 42 may be oriented about 180° apart about the axis 50 of rotation of the common armature 44, although it is contemplated that the plurality of cameras may be in any angular configuration with respect to the rotation axis 50 to allow the cameras to be rotated or to orbit about the axis 50.
  • each camera may be mounted on a corresponding armature by a mounting device.
  • the mounting device 38 connects the camera 28 to the arm 36
  • each camera 40, 42 is mounted to the common armature 44 by a corresponding mounting devices 46, 48.
  • the mounting devices 46, 48 may be a welding seam, a pin and socket engagement, etc., or other commercially available mechanisms, for fixedly mounting the camera to the associated armature and thence to the supporting structure.
  • the mounting devices 38, 46, 48 may be rotatable and optionally mechanically and/or electronically controllable mechanisms, such as commercially available rotating mounting mechanisms, for tilting the corresponding cameras 28, 40, 42 about a central axis of the corresponding mounting devices to different angles, and so to control the focussing of the cameras on the target for improved imaging thereof.
  • tiltable cameras provides an added degree of freedom to the imaging of targets such as the heart of a patient.
  • the detectors may be readily rotated about a portion of the target.
  • the detectors may be rotated about any arbitrary axis, such as an axis passing through the target, as shown in FIG. 4.
  • the compact size of the detectors also allow the detectors to be positioned relatively near the target and rotatable about an axis and directed to the target. Accordingly, multiple detectors may be focused on the target for improved imaging and less distortion.
  • the cameras 40, 42 are tilted at an angle 52 of about 25° below a plane 54 in FIG. 5, and titled about 90° below the plane 54 in FIG. 6.
  • the configuration of cameras 40, 42 to substantially face each other provides complete angular sampling for SPECT applications.
  • each camera 40, 42 may be rotated independently and/or rotated to distinct tilt angles. By using a plurality 40, 42 of cameras rotated to distinct tilt angles, a greater range of projections are utilized, and so distortions associated with insufficient data are minimized and system sensitivity is increased.
  • the cameras 40, 42 are in two positions about 180° degrees apart, and with each camera 40, 42 having a corresponding tilt angle 52 of about 25°.
  • each of cameras 40, 42 has a slant angle collimator having a slant angle of about 45°, the configuration of cameras 40, 42 in FIG. 5 produces an effective slant angle of about 70° for scans of the target.
  • imaging samples of, for example, the heart may be obtained from a variety of angles, with the angles set to be either large or small.
  • the variable tilt angles allow for smaller viewing angles to be employed by the detectors and/or the collimators, with reduced distortion to provide improved accuracy in the data gathering by the detectors.
  • the ability to tilt and to rotate the detectors about an axis and directed toward a target provides the disclosed gamma camera with the ability to cover the same or more directional aspects of the target than prior art devices. The amount and quality of the imaging data is thus improved.
  • the configuration of cameras 40, 42 allows for scans and imaging of objects which can be completely enclosed by the orbit of the cameras.
  • improved imaging of the brain as well as of individual breasts in mammography may be performed, in which the cameras 40, 42 may function as a SPECT device with complete angular sampling.
  • brain imaging with such cameras 40, 42 having tilt angles set to about 90° may be performed using SPECT.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Medical Informatics (AREA)
  • Physics & Mathematics (AREA)
  • Biomedical Technology (AREA)
  • General Health & Medical Sciences (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Optics & Photonics (AREA)
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  • Radiology & Medical Imaging (AREA)
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Abstract

Cette gamma-caméra présente un détecteur de rayonnement (40, 42) à semi-conducteurs, sensible à un rayonnement gamma, afin de produire des signaux de détection correspondants, utiles dans l'imagerie tomographique d'une cible. On a monté ce détecteur sur une structure de support mobile, afin de faciliter le déplacement de la gamma-caméra. Une armature (44) sert à monter ledit détecteur sur la structure de support mobile et on peut orienter cette armature dans plusieurs positions, afin de positionner le détecteur selon plusieurs orientations autour de la cible (16). On peut également utiliser un dispositif de montage pivotant et possédant un axe central, afin de monter de façon pivotante le détecteur sur l'armature et orienter celui-ci selon plusieurs angles inclinés. Un collimateur d'angle incliné constitue une fenêtre angulaire destinée à la réception du rayonnement gamma. Dans un autre mode de réalisation, on utilise un collimateur à trous parallèles afin de constituer une fenêtre de réception du rayonnement gamma. Au moins une armature peut pivoter autour d'un axe et au moins un détecteur de rayonnement à semi-conducteurs est relié à une armature et répond à la commande de pivotement pour tourner autour de la cible et détecter le rayonnement gamma à partir de celle-ci.
PCT/US1997/017224 1996-10-17 1997-09-25 Petite camera pivotante de tomographie Ceased WO1998016852A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US73295996A 1996-10-17 1996-10-17
US08/732,959 1996-10-17

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WO1998016852A1 true WO1998016852A1 (fr) 1998-04-23

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Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2002075358A1 (fr) 2001-03-15 2002-09-26 Koninklijke Philips Electronics Nv Camera gamma a detecteurs rotatifs pour taux d'echantillonnage angulaire variable
WO2002039142A3 (fr) * 2000-11-08 2002-11-21 Koninkl Philips Electronics Nv Correction en fonction de la sensibilite en profondeur d'une camera gamma collimatee a plaques rotatives
EP1424939A4 (fr) * 2001-03-30 2005-05-18 Univ Duke Tomographie par emission et opacite specifique de l'application
US7601966B2 (en) 2006-06-28 2009-10-13 Spectrum Dynamics Llc Imaging techniques for reducing blind spots
US8837793B2 (en) 2005-07-19 2014-09-16 Biosensors International Group, Ltd. Reconstruction stabilizer and active vision
US8894974B2 (en) 2006-05-11 2014-11-25 Spectrum Dynamics Llc Radiopharmaceuticals for diagnosis and therapy
US8909325B2 (en) 2000-08-21 2014-12-09 Biosensors International Group, Ltd. Radioactive emission detector equipped with a position tracking system and utilization thereof with medical systems and in medical procedures
US9040016B2 (en) 2004-01-13 2015-05-26 Biosensors International Group, Ltd. Diagnostic kit and methods for radioimaging myocardial perfusion
US9275451B2 (en) 2006-12-20 2016-03-01 Biosensors International Group, Ltd. Method, a system, and an apparatus for using and processing multidimensional data
US9316743B2 (en) 2004-11-09 2016-04-19 Biosensors International Group, Ltd. System and method for radioactive emission measurement
US9370333B2 (en) 2000-08-21 2016-06-21 Biosensors International Group, Ltd. Radioactive-emission-measurement optimization to specific body structures
US9470801B2 (en) 2004-01-13 2016-10-18 Spectrum Dynamics Llc Gating with anatomically varying durations
US9943274B2 (en) 2004-11-09 2018-04-17 Spectrum Dynamics Medical Limited Radioimaging using low dose isotope
US10964075B2 (en) 2004-01-13 2021-03-30 Spectrum Dynamics Llc Gating with anatomically varying durations

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5365069A (en) * 1993-06-02 1994-11-15 The State Of Israel, Atomic Energy Commission, Soreq Nuclear Research Center Light weight γ-camera head and γ-camera assemblies containing it
FR2715554A1 (fr) * 1994-02-02 1995-08-04 Sopha Medical Gamma caméra à bras tournant.
WO1996020412A1 (fr) * 1994-12-23 1996-07-04 Digirad Gamma-camera a semi-conducteurs et systeme d'imagerie medicale

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5365069A (en) * 1993-06-02 1994-11-15 The State Of Israel, Atomic Energy Commission, Soreq Nuclear Research Center Light weight γ-camera head and γ-camera assemblies containing it
FR2715554A1 (fr) * 1994-02-02 1995-08-04 Sopha Medical Gamma caméra à bras tournant.
WO1996020412A1 (fr) * 1994-12-23 1996-07-04 Digirad Gamma-camera a semi-conducteurs et systeme d'imagerie medicale

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
EISEN Y ET AL: "A GAMMA CAMERA BASED ON CDTE DETECTORS", NUCLEAR INSTRUMENTS & METHODS IN PHYSICS RESEARCH, SECTION - A: ACCELERATORS, SPECTROMETERS, DETECTORS AND ASSOCIATED EQUIPMENT, vol. 380, no. 1/02, 1 October 1996 (1996-10-01), AMSTERDAM NL, pages 474 - 478, XP002038731 *

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8909325B2 (en) 2000-08-21 2014-12-09 Biosensors International Group, Ltd. Radioactive emission detector equipped with a position tracking system and utilization thereof with medical systems and in medical procedures
US9370333B2 (en) 2000-08-21 2016-06-21 Biosensors International Group, Ltd. Radioactive-emission-measurement optimization to specific body structures
WO2002039142A3 (fr) * 2000-11-08 2002-11-21 Koninkl Philips Electronics Nv Correction en fonction de la sensibilite en profondeur d'une camera gamma collimatee a plaques rotatives
US6603123B1 (en) 2000-11-08 2003-08-05 Koninklijke Philips Electronics, N.V. Correction for depth-dependent sensitivity in rotating slat-collimated gamma camera
WO2002075358A1 (fr) 2001-03-15 2002-09-26 Koninklijke Philips Electronics Nv Camera gamma a detecteurs rotatifs pour taux d'echantillonnage angulaire variable
US6593576B2 (en) 2001-03-15 2003-07-15 Koninklijke Philips Electronics, N.V. Variable angular sampling rate for rotating slat-hole detectors of gamma cameras
EP1424939A4 (fr) * 2001-03-30 2005-05-18 Univ Duke Tomographie par emission et opacite specifique de l'application
US7609808B2 (en) 2001-03-30 2009-10-27 Duke University Application specific emission and transmission tomography
US10964075B2 (en) 2004-01-13 2021-03-30 Spectrum Dynamics Llc Gating with anatomically varying durations
US9470801B2 (en) 2004-01-13 2016-10-18 Spectrum Dynamics Llc Gating with anatomically varying durations
US9040016B2 (en) 2004-01-13 2015-05-26 Biosensors International Group, Ltd. Diagnostic kit and methods for radioimaging myocardial perfusion
US9943278B2 (en) 2004-06-01 2018-04-17 Spectrum Dynamics Medical Limited Radioactive-emission-measurement optimization to specific body structures
US9316743B2 (en) 2004-11-09 2016-04-19 Biosensors International Group, Ltd. System and method for radioactive emission measurement
US9943274B2 (en) 2004-11-09 2018-04-17 Spectrum Dynamics Medical Limited Radioimaging using low dose isotope
US10136865B2 (en) 2004-11-09 2018-11-27 Spectrum Dynamics Medical Limited Radioimaging using low dose isotope
US8837793B2 (en) 2005-07-19 2014-09-16 Biosensors International Group, Ltd. Reconstruction stabilizer and active vision
US8894974B2 (en) 2006-05-11 2014-11-25 Spectrum Dynamics Llc Radiopharmaceuticals for diagnosis and therapy
US7601966B2 (en) 2006-06-28 2009-10-13 Spectrum Dynamics Llc Imaging techniques for reducing blind spots
US9275451B2 (en) 2006-12-20 2016-03-01 Biosensors International Group, Ltd. Method, a system, and an apparatus for using and processing multidimensional data

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