Positron computed tomography scanner

Abstract: A positron CT scanner comprises a plurality of detectors (110) arranged in multi-layered rings and slice diaphragms (130) for restricting the visual fields of the detectors, so that the visual fields intersect a set axis during a scan. The spacing between diaphragms substantially corresponds to a certain number of detector cells, each of which can determine the positions of incident rays in the direction of the set axis during a scan. The slice diaphragms (130) are movable relative to the detector cells (110) in the direction of the set axis during a scan.

Description: The invention relates to a positron computed tomography (CT) scanner. Positron CT scanners, or devices for what is called PET (Positron Emission Tomography) are known (S.E. Derenzo et., IEEE Trans. Nucl. Sci., NS-26, No. 2:2790-2793, 1979, etc.). These devices are used for dosing medicines to patients, and such medicines are labelled by radioactive isotopes to image there internal distributions in the patients. In such PET a number of γ (gamma) ray detectors are arranged in rings for the detection by coincidence counting a pair of annihilating photons (0.51 MeV) emitted in directions opposite to each other by the pair annihilation of a positron and an electron. Multi-layers of detector rings are provided, and an intra-ring image can be formed by means of the coincidence counting of the detectors belonging to one ring, while an inter-ring image can be obtained by means of the coincidence counting of adjacent ones of the rings. Accordingly a PET scanner having j layers of detector rings can provide tomographic images of 2j-1 layers at once. A slice septum (collimator) is provided between one of the detector rings and its adjacent one for shielding unnecessary γ rays and internal scattered γ rays, whereby unnecessary counting by the detectors is decreased to reduce counting losses and accidental coincidences. The resolving power is determined mostly by an area of a photon incident surface of a detector (BGO scintillator). The sectional resolving power of the current devices has reached 3 - 5 mm (full width at half maximum value). FIG. 1 is a schematic sectional view of a conventional PET scanner. Each γ ray detector 110 includes both a scintillator 111 and a photomultiplier 112 and these detectors are arranged in rings laid one above another, and shield collimators 120 are provided above the top ring and below the bottom ring. The central axis of the rings is shown as X in FIG. 1. Slice septa 130 are arranged so as to restrict detection fields of the γ ray detectors 110 vertically to the central axis. Generally one slice septum 130 is provided per one layer of γ ray detectors 110. The γ ray shielding effect of the slice septa 130 can reduce noise components as described above. That is, in the case of coincidence counting by two γ ray detectors 110, as shown in FIG. 1, a pair of γ rays from one radioisotope 141 are incident on the γ ray detectors 110 1 , 110 2 ; γ rays from two radioisotopes 142, 143 are concurrently incident by accident on the γ ray detectors 110 3 , 110 4 ; or one of a pair of γ rays from one radioisotope 144 being detected by the γ ray detector 110 6 , the other of the γ rays being scattered by a scatterer 150 and detected by the γ ray detector 110 5 . All the coincidences other than those of the γ rays from the radioisotope 141 are noise. The slice septa 130 for shielding γ rays restrict the detection fields of the γ ray detectors 110 to reduce such noise components. But as the respective γ ray detectors 110 are increasingly more miniaturized to make an interval between each of the slice septa 130 and its adjacent one narrower for the improvement of a resolving power, the γ ray detecting efficiency is lowered proportionally to a square of an interval between the slice septa 130. Accordingly it tends to take much time for counting to form a sufficiently precise image. As a countermeasure to this, so-called three-dimensional PET has been recently studied. In the three-dimensional PET, no slice septa are provided to count not only intra-coincidences of respective detector rings and inter-coincidences between adjacent ones of the detector rings, but also coincidences between ones of the detector rings remote from each other are counted to obtain images at respective slices to restore an image. However, such three-dimensional PET, which acquires and processes three-dimensional data, has a disadvantage of the above-mentioned quite high noise because of not using slice septa. In the case such three-dimensional PET including the conventional slice septa provided between detector rings is realized, the numerical aperture of the γ ray detectors 110 is comparatively large, and inevitably the slice septa 130 have to be thinned and small-sized. Then the γ ray shielding effect of the slice septa 130 is lowered with the result that the above-mentioned accidental coincidences and scattered coincidences are adversely acquired in data, and sharp image cannot be obtained. The invention aims to solve the above-described problems. The invention aims to provide a positron CT scanner which can effectively remove noise in the case that position resolving power of the detectors are improved to raise a resolving power, and in the case that three-dimensional data acquisition and processing are performed. According to the invention there is provided a positron CT scanner comprising a plurality of detectors for performing a detecting operation, the detectors being disposed in a multi-layer ring arrangement around a predetermined axis so that the detection fields thereof are directed toward the predetermined axis; slice septa means comprising a plurality of portions offset with respect to one another in the direction of the predetermined axis for restricting respective detection fields; and driving means for driving the slice septa means, characterised in that the driving means is operable during the detecting operation to move the portions in opposing directions along the direction of the predetermined axis so as to adjust the detection fields in dependence on the region being scanned. In a positron CT scanner embodying the invention to be described hereinafter there are provided a plurality of detectors (e.g., BGO scintillators and photomultipliers) each having one detection cell or a plurality of detection cells for detecting incident photons and arranged in multi-layers rings of which a central axis is a predetermined axis; slice septa for restricting detection fields of the detectors so that the detection fields cross the predetermined axis, the slice septa spacing the detectors from each other in the direction of the axis at an interval a total of which substantially corresponds to a total of a size of the detection cells in the direction of the predetermined axis; means for driving the slice septa (e.g., in piston motions and rotary motions); means for pre-processing outputs of associated ones of the detectors and selecting two photons generated by a pair annihilation of a positron and an electron (e.g., discriminators, coincidence circuits and switches); and means for restoring a sectional material distribution of a detected sample (e.g. a computer system and an image display). The slice septa are moved during a counting operation of photons. In order to make the slice septa relatively movable for the detectors, the slice septa themselves are movable in the direction of the predetermined axis, or are able to perform precessions. Otherwise, positions of the slice septa may be changed continuously or by steps in the direction of the predetermined axis, and additionally on rotation around the predetermined axis. The interval between each of the slice septa and its adjacent one substantially corresponds to a total of a plurality of detectors of a size in the direction of the predetermined axis. As a result, it is not necessary to thin the slice septa. Consequently with a numerical aperture of the detectors retained, oblique incidence of γ rays which is a cause of accidental coincidences can be prevented. Data acquisition is possible with efficient use of pair annihilations of electrons and positrons, and with improved S/N ratios. Furthermore, the slice septa are moved during a counting operation with respect to their associated detectors in the direction of the predetermined axis (central axis). Consequently the prevention of obliquely incident γ rays and each detecting efficiency of the detectors can be uniform among the respective detectors. The above-described functions make it possible to shorten a counting time and to improve its resolution power of the positron CT scanner. EP-A-141,135 describes an emission computed tomograph in which a plurality of circular arrays of radiation detectors are arranged circumferentially about and axially of a patient to be examined, with a collimator ring rotatably supported and interposed between the radiation detectors and the patient so that emitted radiation from the patient causes some of the radiation detectors to produce corresponding outputs. The collimator ring is rotated so that radiation from the patient is detected in all directions. The present invention will become more fully understood from the detailed description of embodiments given hereinbelow with reference to the accompanying drawings which are given by way of illustration only, and thus are not to be considered as limiting the present invention. Further scope of applicability of the present invention will become apparent to those skilled in the art from the detailed description given hereinafter. It should be understood that the detailed description and specific examples, while indicating preferred embodiments of the invention, are given by way of illustration only, since various changes and modifications within the scope of the invention will become apparent to those skilled in the art from this detailed description. In the drawings: FIG. 1 is an explanatory view of a conventional positron CT scanner. FIG. 2 is a conceptual view of the entire positron CT scanner embodying the invention. FIG. 3A is view of the positron CT scanner according to a first embodiment of this invention explaining the structure and function. FIG. 3B is a perspective view of slice septa according to the first embodiment of this invention FIG. 4A is view of the positron CT scanner according to a second embodiment of this invention explaining the structure and function. FIG. 4B is a perspective view of slice septa according to the second embodiment of this invention FIG. 5A is view of the positron CT scanner according to a third embodiment of this invention explaining the structure and function. FIG. 5B is a perspective view of slice septa according to the third embodiment of this invention. FIG. 6A is view of the positron CT scanner according to a fourth embodiment of this invention explaining the structure and function. FIG. 6B is a perspective view of slice septa according to the fourth embodiment of this invention FIG. 7A is view of the positron CT scanner according to a fifth embodiment of this invention explaining the structure and function. FIG. 7B is a perspective view of slice septa according to the fifth embodiment of this invention. FIG. 8A is view of a positron CT scanner explaining the structure and function. FIG. 8B is a perspective view of slice septa of the FIG. 8A scanner. FIG. 9 is a view of an example of the means for driving the slice septa (piston motions) involved in the first embodiment. FIG. 10 is a view of an example of the means for driving slice septa (rotary motions) involved in the second to the sixth embodiments. FIG. 11A is a view of a piston motion of slice septa according to this invention. FIG. 11B is a view of a precession motion of slice septa according to this invention. FIG. 11C is a view of a spiral rotary motion of slice septa according to this invention. FIG. 12A is a view of a layer structure of the detectors of a simulation of the positron CT scanner according to this invention. FIG. 12B is a view of one structure of the slice septa in the simulation. FIG. 12C is a view of another structure of the slice septa in the simulation. FIG. 13A shows the result of the simulation about differential detection efficiencies in FIG. 12A. Structure of septa is shown in FIG. 11A and 12B, and the septa is in no motion. FIG. 13B shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the septa is in no motion. FIG. 13C shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and an amplitude of a constant velocity motion is 20mm. FIG. 13D shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG.11A and 12B, and the amplitude of the constant velocity piston motion is 20mm. FIG. 14A shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and an amplitude of a constant velocity motion is 22mm. FIG. 14B shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the constant velocity piston motion is 22mm. FIG. 14C shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the constant velocity motion is 24mm. FIG. 14D shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the constant velocity piston motion is 24mm. FIG. 15A shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and an amplitude of a sinusoidal motion is 16mm. FIG. 15B shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the sinusoidal piston motion is 16mm. FIG. 15C shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the sinusoidal motion is 18mm. FIG. 15D shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the sinusoidal piston motion is 18mm. FIG. 16A shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and an amplitude of a sinusoidal motion is 22mm. FIG. 16B shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the sinusoidal piston motion is 22mm. FIG. 16C shows the result of the simulation about differential detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of a sinusoidal motion is 24mm. FIG. 16D shows the result of the simulation about integral detection efficiencies in FIG. 12A. The structure of septa is shown in FIG. 11A and 12B, and the amplitude of the sinusoidal piston motion is 24mm. FIG. 17A shows the best result of the simulation about differential detection efficiencies in the constant velocity piston motion of the parallel septa. FIG. 17B shows the best result of the simulation about integral detection efficiencies in the constant velocity piston motion of the parallel septa. FIG. 17C shows the best result of the simulation about differential detection efficiencies in the sinusoidal piston motion of the parallel septa. FIG. 17D shows the best result of the simulation about integral detection efficiencies in the sinusoidal piston motion of the parallel septa. FIG. 18A shows the best result of the simulation about differential detection efficiencies in a precession of the parallel septa. FIG. 18B shows the best result of the simulation about integral detection efficiencies in the precession of the parallel septa. FIG. 18C shows the best result of the simulation about differential detection efficiencies in a rotary motion of a helical septum. FIG. 18D shows the best result of the simulation about integral detection efficiencies in the rotary motion of the helical septum. FIG. 18 is explanatory views of the results of the simulation of FIGs. 11 and 12. Referring now to FIG. 2 there is shown conceptual view of an entire positron CT scanner embodying the invention. This positron CT scanner comprises a photon detecting unit 100, a detected signal pre-processing unit 200, and an image restoring unit 300. The photon detecting unit 100 comprises a number of detectors 110 arranged in multi-layers rings of which the outer shape is cylindrical; slice septa 130 for restricting detection fields of the respective detectors 110 so as to cross the central axis of the cylinder; and means 160 for driving the slice septa 130 in a piston motion toward the central axis or in a rotary motion around the central axis. The detected signal pre-processing unit 200 comprises the same number of discriminators 210 as the detectors each for analyzing an amplitude of an electric signal outputted by each of the detectors 110 (i.e., energy of an incident photon) and selecting candidates of expected event; a coincidence circuit for judging that only two photon have generated in the associated layer, or two adjacent layers, based on the input of a signal of the candidate event selected by the discriminator 210, and informing the image restoring unit 300 of the occurrence of the event; and switches 230 controlled by the coincidence circuits 220 to operate, and provided for each of the outputs of the discriminators 210. Two photons generated by a pair annihilation of a positron and an electron which has taken place in an object-to-be-detected are detected separately as one individual photon by the photon detecting unit 100. These photons are judged to have been generated by a pair annihilation by the detected signal pre-processing unit 200, based on their energy and coincident generation. The image reconstructing unit 300 computes a position of the pair annihilation, based on data of the detectors 130 which have detected the photons as photon detection position information. The unit 300 statistically computes and processes a frequency of occurrences of pair annihilations near one position and presumes a material distribution inside the material-to-be-detected, and then restores this material distribution as image and displays the image on an image display 320. The detected signal pre-processing unit 200 and the image restoring unit 300 are per se known and will not be described in any further detail herein. FIG 3A and 3B are diagrammatic views of the positron CT scanner according to a first embodiment of this invention. FIG. 3A is a sectional view, and FIG. 3B is a perspective view of slice septa 130. In FIG. 3A and 3B, an interval between one of three slice septa 130 and its adjacent one is about 4 times a size of a γ ray detector 110 in the direction of the central axis shown as X thereof, and the slice septa 130 1 - 130 3 perform a piston-motion toward the central axis at an amplitude corresponding to a size of about four detectors 110. In this embodiment, one γ ray detector 110 comprised of scintillator 111 and photomultiplier 112 provides one detection cell. In this embodiment, one sheet of slice septum 130 X is provided for 4 layers of γ ray detectors 110. Even in the case that the γ ray detector 110 is miniaturized, the slice septa 130 will not almostly lower the numerical aperture of the detectors. In other words, the slice septa 130 can be made the thicker, and the effect of their shielding γ ray can be accordingly retained. The slice septa 130 are driven in a piston motion in the direction of the central axis, and the effect of the slice septa 130 shielding the oblique incidence of γ rays, and the detection efficiency can be uniform among the respective γ ray detectors. 110. FIG. 4A and 4B are diagrammatic views of the positron CT scanner according to a second embodiment of this invention. In this embodiment, three slice septa 130 1 - 130 3 are inclined at an angle  to a central axis so as to perform a precession around the central axis shown as X. Equivalently in this arrangement as well, the slice septa 130 move with respect to their associated γ ray detectors 110 in the direction of the central axis, and the same effects can be achieved as in the first embodiment. In this embodiment, one γ ray detector 110 does not correspond to one detection cell. A scintillator 111 has a plurality of sections, and respective sections and respective elements of a photomultiplier 112 provide a plurality of detection cells. This photomultiplier 112 is exemplified by a multi-anode type photomultiplier. FIG. 5A and 5B are diagrammatic views of the positron CT scanner according to a third embodiment of this invention. In this embodiment, three slice septa 130 1 - 130 3 are parallel with one another but are not normal to a central axis, and additionally are rotatable around the central axis shown as X. In this case, the slice septa 130 1 - 130 3 can make a piston motion at an amplitude corresponding to a plurality of detection cells provided by γ ray detectors 110 relative to the detection cells. Accordingly the same effects as in the preceding embodiments can be produced. One detection cell may comprise one scintillator 111 and one photomultiplier as in the first embodiment, and otherwise one section of scintillator 111 and one element (picture element) of a multi-anode type photomultiplier 112 as in the second embodiment. FIG. 6A and 6B are diagrammatic views of the positron CT scanner according to a fourth embodiment of this invention. In this embodiment, slice septa 130 are provided in a helix and is rotatable around a central axis. When the slice septa 130 is rotated, they move relative to the respective detection cells in the direction of the central axis. FIG. 7A and 7B are diagrammatic views of the positron CT scanner according to a seventh embodiment of this invention. In this embodiment, annular slice septa 130 undulate in the direction of a central axis. By rotating the slice septa 130 around a central axis, the slice septa 130 are caused to make a piston motion with respect to respective detection cells. This embodiment is characterized in that the slice septa 130 can make a piston motion without reversing a rotational direction. FIG. 8A and 8B are diagrammatic views of another positron CT scanner. In this scanner, each set of slice septa is provided in the form of sections of an annular plate 130 11 - 130 13 , 130 21 - 130 23 , 130 31 , - 130 33 . Positions of the slice septa 130 in the direction of a central axis can be displaced by steps by rotating the slice septa 130. In this scanner, the slice septa 130 do not continuously move, as they do in the above described first to the fifth embodiments, but the effects intended by this invention can be sufficiently produced. Especially it can be equivalent to the case that one slice septum is provided between each of detection cells and its adjacent one to make an interval between each of three sets of slice septa 130 11 - 130 13 , 130 21 - 130 23 , 130 31 - 130 33 and its adjacent set correspond to three detector cells. Next, means for driving the slice septa will be explained. The drive mode of the slice septa includes piston motions in the direction of the central axis, and rotary motions around the central axis. FIG. 9 shows one example of driving means for the piston motions. The slice septa 130 comprise a plurality of annular plate members 130 1 - 130 3 , and a holder 131. The holder 131 is mechanically connected to a driving unit 160. The driving unit 160 comprises a driving motor 161, a gear 162, a pinion gear 163, and a guide rail 164. The driving motor 161 is rotated to drive all the slice septa 130 to make a piston motion in the direction of the central axis. FIG. 10 shows one example of means for driving means for the rotary motions. The slice septa 130 comprise a plurality of annular plate members 130 1 - 130 3 , and a holder 131. The holder is mechanically connected to a driving unit 160. The driving unit 160 comprises a driving motor 161, a pulley 165, a belt 166 and a bearing gear 167. The driving motor 161 is rotated to drive all the slice septa 130 to make a rotary motion around the central axis. This example has been explained in connection with the drive of the third embodiment described above, but can drive the other embodiments which make rotary motions. FIGs. 11A to 11C show modes of the drive of the slice spectra 130. A first drive mode is a piston motion and is shown in FIG. 11A. A second drive mode is a sinusoidal piston motion and is shown also in FIG. 11A. A third drive mode is an axis swaying drive, i.e., a precession and is shown in FIG. 11B. A fourth drive mode is a spiral rotary motion and is shown in FIG. 11C. As shown in FIG. 12A, the layer structure of γ ray detectors includes 16 layers (i=0-15), and a ratio of a γ-ray detectors arranging pitch vs. an interval between slice septa 130 is 4 as shown in FIG. 12B. The results are shown in FIGs. 13A to 18D. In FIGs. 13A to 18D, the numbers 0 to 15 on the horizontal axis indicate the numbers of the opposed groups of γ ray detectors 114 (refer to FIG. 12A). The drawings (Dif) on the left side show detection sensitivities of the respective opposed γ ray detectors, and the drawings (Int) on the right side show integrated values of the detection sensitivities of the 0-th to i-th detectors. In the respective drawings, the four curves correspond to four γ ray detectors within one interval between slice septa. In the drawings showing the integrated values on the right side, cases in which the four curves better conform to one another have better characteristics. FIGs. 13A to 14D show in contrast cases of the constant velocity piston motion as in FIG. 11A and of no motion. FIGs. 13A and 13B show the case of no motion (amplitude: 0 mm), and FIGs. 13C and 13D show the case of the piston motion at an amplitude of 20 mm. FIGs. 14A and 14B show the cases of the piston motion at an amplitude of 22 mm, and FIGs. 14C and 14D show the cases of the piston motion at an amplitude of 24 mm. It is seen that the best characteristics can be obtained when an amplitude, and an interval of the slice septa 130 agree with each other. FIGs 15A to 16D show cases of the sinusoidal piston motions respectively at amplitudes of 16, 18, 22, 24 mm. It is seen that in these cases the best characteristics can be obtained when the slice septa 130 are moved in the sinusoidal piston motion at an amplitude corresponding to about 75 % of an interval of the slice septa 130. FIGs. 17A to 18D show in contrast characteristics of the respective drive modes at amplitude conditions producing the best results. From the invention thus described, it will be obvious that the invention may be varied in many ways. Such variations are not to be regarded as a departure from the scope of the invention, and all such modifications as would be obvious to one skilled in the art are within the scope of the following claims.

Claims: A positron CT scanner comprising a plurality of detectors (110) for performing a detecting operation, the detectors being disposed in a multi-layer ring arrangement around a predetermined axis so that the detection fields thereof are directed toward the predetermined axis; slice septa means (130) comprising a plurality of portions (130 1 , 130 2 , 130 3 ) offset with respect to one another in the direction of the predetermined axis for restricting respective detection fields; and driving means (160) for driving the slice septa means, characterised in that the driving means (160) is operable during the detecting operation to move the portions (130 1 , 130 2 , 130 3 ) in opposing directions along the direction of the predetermined axis (110) so as to adjust the detection fields in dependence on the region being scanned. A positron CT scanner according to claim 1, wherein the slice septa means (130) comprise a plurality of annular disk members (130 1 , 130 2 , 130 3 ) spaced along a central axis, the scanner further comprising a holder (131) for holding the disk members to maintain a fixed relative positional relationship between the disk members. A positron CT scanner according to claim 2, wherein the central axis of the annular disk members (130 1 , 130 2 , 130 3 ) is coincident with the predetermined axis of the detector ring arrangement. A positron CT scanner according to claim 2, wherein the central axis of the annular disk members (130 1 , 130 2 , 130 3 ) is oblique to the predetermined axis of the detector ring arrangement. A positron CT scanner according to claim 1, wherein the slice septa means (130) comprise a plurality of annular disk members (130 1 , 130 2 , 130 3 ) spaced along the predetermined axis, each of the disk members being centred on the predetermined axis and having a central axis oblique to the predetermined axis by substantially the same angle, the scanner further comprising a holder (131) for holding the disk members to maintain a fixed relative positional relationship between the disk members. A positron CT scanner according to claim 4 or 5, wherein the driving means (160) is operable to rotate the slice septa means (130) about the predetermined axis, the driving means thereby driving the portions (130 1 , 130 2 , 130 3 ) in said opposing directions along the direction of the predetermined axis. A positron CT scanner according to claim 1, wherein the slice septa means (130) comprise a single plate member formed as a helix along the predetermined axis; the scanner further comprising a holder (131) for holding the plate member so that different portions thereof adjust respective detection fields of the detectors. A positron CT scanner according to claim 7, wherein the driving means (160) is operable to rotate the helical plate member about the predetermined axis. A positron CT scanner according to claim 1, wherein the slice septa means (130) comprise a plurality of undulating annular members spaced along the predetermined axis, the scanner further comprising a holder (131) for holding the annular members to maintain a fixed relative positional relationship between the annular members. A positron CT scanner according to claim 9, wherein the driving means (160) is operable to rotate the undulating annular members (130) about the predetermined axis. A positron CT scanner according to claim 1, wherein the slice septa means (130) comprise a plurality of curved sections offset with respect to one another about and being spaced along the predetermined axis, the scanner further comprising a holder (131) for holding the curved section to maintain a fixed relative positional relationship between the curved sections. A positron CT scanner according to any preceding claim, wherein each detector (110) comprises one scintillator (111) and one photodetector (112), and thereby provides one detecting cell. A positron CT scanner according to any of claims 1 to 11, wherein each detector comprises a scintillator (111) divided in a plurality of sections and one photodetector (112), and thereby provides a plurality of detecting cells corresponding in number to the plurality of sections. A positron CT scanner according to claim 13, wherein the photodetector (112) includes means for determining incidence positions. A positron CT scanner according to claim 12 or 13 or 14, wherein each detecting cell (110) comprises means for converting a detected incident photon into an electric signal corresponding to energy thereof. A positron CT scanner according to any preceding claim, further comprising means (200) for processing output signals of the detectors, and means (300) for restoring a sectional material distribution of a detected object.

Inventors: SATOH NAKAHIRO, SHIMIZU KEIJI, TANAKA EIICHI, SATOH, NAKAHIRO, SHIMIZU, KEIJI, TANAKA, EIICHI, Satoh, Nakahiro, c/o Hamamatsu Photonics K.K., Shimizu, Keiji, c/o Hamamatsu Photonics K.K., TANAKA, EIICHI, C/O HAMAMATSU PHOTONICS K.K.
Applicants: HAMAMATSU PHOTONICS KK, HAMAMATSU PHOTONICS K.K.
Application year: 1992
Main classification: A61B6
IPC codes: G01T1, A61B6