Source: https://patents.google.com/patent/JP2004144529A/en
Timestamp: 2020-02-26 11:16:52
Document Index: 478094146

Matched Legal Cases: ['art 56', 'art) 56', 'art 56', 'art 56', 'art 56', 'art 56', 'art 56', 'art 56', 'art 56', 'art 56', 'art 52', 'art, 8']

JP2004144529A - Radiation inspection device - Google Patents
Radiation inspection device Download PDF
JP2004144529A
JP2004144529A JP2002307785A JP2002307785A JP2004144529A JP 2004144529 A JP2004144529 A JP 2004144529A JP 2002307785 A JP2002307785 A JP 2002307785A JP 2002307785 A JP2002307785 A JP 2002307785A JP 2004144529 A JP2004144529 A JP 2004144529A
JP2002307785A
JP4093013B2 (en
上野　雄一郎
北口　博司
小嶋　進一
柳田　憲史
梅垣　菊男
横井　一磨
雨宮　健介
2002-10-23 Application filed by Hitachi Ltd, 株式会社日立製作所 filed Critical Hitachi Ltd
2002-10-23 Priority to JP2002307785A priority Critical patent/JP4093013B2/en
2004-05-20 Publication of JP2004144529A publication Critical patent/JP2004144529A/en
2008-05-28 Publication of JP4093013B2 publication Critical patent/JP4093013B2/en
[PROBLEMS] To improve the accuracy of an image and to easily replace a failed radiation detector.
An imaging device of a radiation inspection apparatus according to the present invention includes a plurality of detector units, an annular detector support member, and an X-ray source circumferential moving device. The detector unit 4 has nine radiation detectors 5 provided on one surface of a support substrate 6, a connector portion 7 provided on the support substrate 6, and a large number of detector units 8 arranged in the circumferential direction and the axial direction of the detector support member 8. . Each detector unit 4 is detachably mounted on the detector support 23. The plurality of radiation detectors 5 provided in the detector unit 4 are arranged in three layers in the radial direction of the detector support member 8 and in three rows in the axial direction of the detector support member 8. Since the radiation detectors are arranged in three layers in the radial direction, the radiation detection position in the radial direction can be finely recognized. Further, since the detector unit 4 is detachably installed, replacement of the failed radiation detector 5 is simplified.
The present invention relates to a radiation inspection apparatus, and in particular, to a radiation two-dimensional imaging apparatus, X-ray computed tomography (hereinafter, referred to as X-ray CT), positron emission CT (positron emission CT). Computed tomography (Position Emission Computed Tomography, hereinafter referred to as PET) and single photon emission CT (Single Photon Emission Computed Tomography, hereinafter referred to as PET). The present invention relates to a radiation inspection apparatus suitable for adapting to the above.
Representative examples of a radiological examination apparatus that is a technique for non-invasively imaging the function and form inside the body of a subject to be examined as a subject include a radiation two-dimensional imaging apparatus, X-ray CT, PET, and SPECT.
The PET test shows that the radionuclide positron emitting nuclide ( Fifteen O, Thirteen N, 11 C, 18 F) is administered to a patient to be examined, and a test is conducted to determine at which site in the body the PET drug is consumed in large amounts. PET inspection
This is an act of detecting, with a radiation detector, γ-rays emitted from the body of the subject due to the PET drug. Specifically, a positron emitted from a radionuclide contained in a PET drug is annihilated by binding to an electron of a nearby cell (cancer cell), and at that time, a pair of γ-rays having energy of 511 keV ( Γ rays) are emitted. These gamma rays are emitted in directions substantially opposite to each other (180 ° ± 0.6 °). If this paired gamma ray is detected by a radiation detector, it is possible to know which two radiation detectors have emitted a positron. By detecting such a large number of γ-ray pairs, a place where a large amount of the PET drug is consumed can be determined. Then, for example, when a PET drug manufactured by combining a positron-emitting nuclide with a sugar is used, it is possible to find a cancer lesion with a severe sugar metabolism. An example of a radiation inspection apparatus used for PET is described in Patent Document 1. In addition, the obtained data is converted into data of each voxel by a filtered back projection method (Filtered Back Projection Method) described in Non-Patent Document 1. Positron emission nuclide used for PET inspection ( Fifteen O, Thirteen N, 11 C, 18 F) has a half-life of 2 to 110 minutes.
SPECT is a radionuclide single photon emitting nuclide ( 99 Tc, 67 Ga, 201 Tl, etc.) and a radiopharmaceutical (SPECT drug) containing a substance (eg, sugar) having a property of accumulating in a specific tumor or a specific molecule is administered to a subject, and γ-rays released from the radionuclide are administered. Detect with a radiation detector. The energy of γ-rays emitted from single photon emitting nuclides often used during inspection by SPECT is around several hundred keV. In the case of SPECT, since a single γ ray is emitted, the angle of the γ ray incident on the radiation detector cannot be obtained. Thus, angle information is obtained by detecting only γ-rays incident from a specific angle with a radiation detector using a collimator. SPECT is a test method that detects γ-rays generated in the body due to a SPECT drug and identifies a place that consumes a large amount of the SPECT drug. An example of a radiation inspection apparatus used for SPECT is described in Patent Document 2. Also in the case of SPECT, the obtained data is converted into data of each voxel by a method such as filtered back projection. It should be noted that a transmission image may be captured even in SPECT. Used for SPECT 99 Tc, 67 Ga, 201 Tl is 6 hours to 3 days longer than the half-life of the radionuclide for PET.
JP-A-7-20245
JP-A-9-5441
IEEE Transactions on Nuclear Science, NS-21, Volumes 228-229.
For example, it is desired to further improve the diagnostic accuracy of the position and size of an affected part such as a malignant tumor, and it is required to improve the accuracy of an image including the affected part created by such a radiological examination apparatus. Another important issue is that a failed radiation detector can be replaced in a short time.
An object of the present invention is to provide a radiation inspection apparatus that can improve the accuracy of a created image and can easily replace a failed radiation detector.
The feature of the present invention that achieves the above object is that a detector unit is detachably attached to a detector support member, and the detector unit has a plurality of radiation detectors for detecting radiation, and Another radiation detector for detecting radiation passing through the radiation detector is provided.
Since another radiation detector for detecting radiation passing through a certain radiation detector is provided, the radiation emitted from the subject can be detected by the above-mentioned one radiation detector or another radiation detector, and is opposed to the subject. It is possible to accurately confirm the position at which the radiation has reached from the certain radiation detector in the depth direction (the position where the radiation has been detected). For this reason, an accurate image showing the state of the inside of the subject can be obtained. Further, since the detector unit is detachably attached to the detector support member, the failed radiation detector can be easily replaced.
A radiation inspection apparatus according to a preferred embodiment of the present invention will be described below with reference to FIGS. The radiation inspection apparatus 1 according to the present embodiment is used for PET inspection. The radiation inspection apparatus 1 includes an imaging device 2, a signal processing device 40, a tomographic image creation device 35, an examinee holding device 18, a driving device control device 21, and an X-ray source control device 22. The examinee holding device 18 is provided at the upper end of the bed support 19 so that the bed 20 can be moved in the longitudinal direction of the bed 20.
The imaging device 2 includes a casing 3, a number of detector units 4, an annular detector support member 8, and an X-ray source circumferential moving device 13. As shown in FIGS. 3 and 4, the detector support member 8 has an annular detector support portion 23 attached to the support member 39 and a cover member 24. The cover member 24 is attached to the detector support 23 so as to cover the signal discrimination unit storage space 44 formed in the detector support 23.
The X-ray source circumferential moving device 13 includes a guide rail 12 and an X-ray source device 14. The annular guide rail 12 is attached to the examinee holding device 18 on the side of the detector support member 8, specifically, the side of the detector support 23 so as to surround the hole 41 into which the bed 20 is inserted. Can be The X-ray source device 14 includes an X-ray source driving device 15, a telescopic arm 16, and an X-ray source 17. The X-ray source driving device 15 is movably mounted on the guide rail 12. Although not shown, the X-ray source driving device 15 has a pinion that meshes with a rack of the guide rail 12, and includes a motor that rotates the pinion via a speed reduction mechanism. The telescopic arm 16 is attached to a casing (not shown) of the X-ray source driving device 15 and can expand and contract in the horizontal direction. The X-ray source 17 is attached to the distal end of the telescopic arm 16.
The X-ray source 17 has a known X-ray tube, not shown. This X-ray tube includes an anode, a cathode, a current source for a cathode, and a voltage source for applying a voltage between the anode and the cathode in an outer cylinder. The cathode is a tungsten filament. By passing a current from the current source to the cathode, electrons are emitted from the filament. The electrons are accelerated by a voltage (several hundred kV) applied between the cathode and the anode from a voltage source, and collide with a target anode (W, Mo, etc.). X-rays of 80 keV are generated by collision of electrons with the anode. This X-ray is emitted from the X-ray source 17.
The tomographic image creation device 35 includes a computer 36 and a storage device 37. The computer 36 is connected to the coincidence counting device 34, and the storage device 37 is connected to the computer 36. The computer 36 is a tomographic image creation unit. The display device 38 is connected to the computer 36.
As shown in FIGS. 5 and 6, the detector unit 4 is configured such that a plurality of (for example, nine) radiation detectors 5 are provided on one surface of a support substrate 6, and a connector section 7 is provided on the support substrate 6. . The nine radiation detectors 5 are arranged on the support substrate 6 in three rows and three columns. In FIG. 4, “circumferential direction” indicates the circumferential direction of the detector support member 8, “axial direction” indicates the axial direction of the detector support member 8, and “radial direction” indicates the direction of the detector support member 8. This means the radial direction (the same applies to FIGS. 10 and 12). The three radiation detectors 5 arranged in a line in the radial direction of the detector support member 8, that is, the cathode electrodes K1, K2, and K3 of the radiation detectors 5A, 5B, and 5C are connected to the ground wire 45. The ground wire 45 is connected to the connector terminal 7D of the connector section 7. The wiring 46 connected to the anode electrode A1 of the radiation detector 5A is connected to the connector terminal 7A of the connector unit 7. The wiring 47 connected to the anode electrode A2 of the radiation detector 5B is connected to the connector terminal 7B of the connector unit 7. The wiring 48 connected to the anode electrode A3 of the radiation detector 5C is connected to the connector terminal 7C of the connector unit 7. Each of the radiation detectors 5 included in the other two rows is also connected to another connector terminal provided on the connector unit 7. The ground wire 45 and the wirings 46, 47, 48 are all installed in the support substrate 6. The large number of detector units 4 are mounted and held on the detector support unit 23 by fitting the connector terminals such as the connector terminals 7A provided on the respective connector units 11 provided on the detector support unit 23. You. A large number of the detector units 4 surround the hole 41 and are arranged in the circumferential direction and the axial direction of the hole 41. These detector units 4 are detachably attached to the detector support 23.
The casing 3 is attached to the detector support 23 so as to cover these detector units 4 (FIG. 4). The casing 3 is formed so as to extend in the horizontal direction, and forms a hole (through hole) 41 into which the bed 20 is inserted at the time of inspection (FIG. 1).
By installing these detector units 4, a large number of radiation detectors (for example, 10,000 in total) 5 are arranged in the casing 3 inside the annular detector support member 8. The radiation detectors 5 are arranged in multiple layers (for example, three layers) in the radial direction of the detector support member 8 and in a plurality of rows in the axial direction of the detector support member 8. The three radiation detectors 5 (radiation detectors 5A) farthest from the connector unit 7 among the radiation detectors 5 arranged in each detector unit 4 are located at positions closest to the axis of the hole 41. It is called the first-layer radiation detector. The three radiation detectors 5 (radiation detectors 5C) closest to the connector 7 are located farthest from the axis of the hole 41 and are referred to as a third-layer radiation detector. The three radiation detectors 5 (radiation detectors 5B) located between the first and third layers in the detector unit 4 are referred to as a second-layer radiation detector.
The radiation detection device 43 includes the large number of radiation detection units 4 described above. The radiation detection device 43 includes a plurality of radiation detectors 5 arranged in one to three layers in the radial direction of the detector support member 8 and arranged in the axial direction of the detector support member 8.
Representative radiation detectors include semiconductor radiation detectors and scintillators. The scintillator needs to be provided with a photomultiplier tube or the like at the rear of a crystal (BGO, NaI, etc.) as a radiation detection unit, and is not suitable for a stacked arrangement (for example, the above-described three layers). Since the semiconductor radiation detector does not require a photomultiplier tube or the like, it is suitable for a stacked arrangement. In this embodiment, the radiation detector 5 uses a semiconductor radiation detector, and a 5 mm cube serving as a detection unit is made of cadmium tellurium (CdTe). The detector may be made of gallium arsenide (GaAs) or cadmium tellurium zinc (CZT).
The signal processing device 40 includes a signal discrimination device 27, a γ-ray discrimination device 32, and a coincidence counting device 34. The signal discriminating device 27 is provided for each radiation detector 5 in the first layer. Further, a γ-ray discriminating device 32 is provided for each of the second and third radiation detectors 5. The three signal discriminators 27 and the six γ-ray discriminators 32 are installed on one substrate 26. The signal discrimination unit 25 is constituted by three signal discrimination devices 27 and six γ-ray discrimination devices 32 installed on the substrate 26. The substrate 26 is attached to the unit support member 66. Each signal discrimination unit 25 provided for each detector unit 4 is attached to a unit support member 66 disposed in the signal discrimination unit storage space 44 as shown in FIG. The unit support member 66 is attached to the detector support 23. The signal discrimination unit 25 is held on the detector support member 8 by being installed on the unit support member 66. The substrate 26 can also be directly attached to the detector support 23 as a support substrate without using the unit support member 66.
The signal discriminating device 27 includes a changeover switch 28, a γ-ray discriminating device 32, and an X-ray signal processing device 33, as shown in FIG. The changeover switch 28 has a movable terminal 29 and fixed terminals 30 and 31. The γ-ray discriminating device 32 is connected to the fixed terminal 30, and the X-ray signal processing device 33 is connected to the fixed terminal 31. The connector terminal 7A connected to the first-layer radiation detector 5A comes into contact with the connector terminal 11A provided on the connector section 11 by the connection between the connector section 7 and the connector section 11. The movable terminal 29 is connected to the connector terminal 11A by a wiring 49. The wiring 49 is provided on the unit support member 66. The negative terminal of the power supply 50 is connected to the wiring 46 via the resistor 51, and the positive terminal of the power supply 50 is connected to the radiation detector 5A. The γ-ray discriminating devices 32 in all the signal discriminating devices 27 are connected to the coincidence counting device 34 by the wiring 52. Further, the X-ray signal processing devices 33 in all the signal discriminating devices 27 are connected to the computer 36 by the wiring 53.
Of the six γ-ray discrimination devices 32 provided in the signal discrimination unit 25 except the signal discrimination device 27, three of the γ-ray discrimination devices 32 are connected to the connector terminal 11 </ b> B (not shown) of the connector unit 11 by the wiring 54. Connected to. The connector terminal 11B is in contact with the connector terminal 7B to which the second-layer radiation detector 5B is connected. The remaining three γ-ray discriminating devices 32 are connected to the connector terminals 11C (not shown) of the connector section 11 by other wires 54. The connector terminal 11B is in contact with the connector terminal 7C to which the third-layer radiation detector 5C is connected. The six γ-ray discriminating devices 32 other than the signal discriminating device 27 are connected to the coincidence counting device 34 by wiring 55, respectively. In FIG. 1, the signal discrimination unit 25 and the wires 54 and 56 are displayed outside the detector support member 8, but this is because the signal discrimination device 27 and the γ-ray discrimination device 32 provided in the signal discrimination unit 25. This is because the connection state by the wiring is easily understood. The signal discrimination unit 25 is actually installed in the detector support member 8 as shown in FIGS. 3 and 4, and the wirings 52, 53, and 55 are drawn out of the detector support member 8.
Before specifically describing the radiation inspection in the present embodiment, the principle of radiation detection in the present embodiment will be described. The data of the X-ray CT image (tomographic image including the image of the internal organs and bones of the subject obtained by the X-ray CT) is obtained by converting the X-ray emitted from the X-ray source in a specific direction for a predetermined time. The operation (scanning) of irradiating the subject and detecting X-rays transmitted through the body by the radiation detector is repeated, and is created based on the intensities of the X-rays detected by the plurality of radiation detectors. In order to obtain accurate X-ray CT image data, in an X-ray CT examination, a radiation detector detecting X-rays emits γ-rays emitted from the inside of the subject due to a PET drug. Is preferably not incident. In one radiation detector, the influence of γ-rays can be neglected if the irradiation time of X-rays to the subject is shortened in accordance with the incidence rate of γ-rays. Shortened. In order to determine the X-ray irradiation time T, first, the incidence rate of γ-rays to one radiation detector is considered. In the PET test, N (Bq) is the radioactivity in the body based on the PET drug administered to the subject, A is the transmissivity of the generated γ-rays in the body, and B is the incidence rate obtained from the solid angle of one radiation detector. , And the sensitivity of the detection element is C, the rate α (number / sec) of γ-rays detected by one radiation detector is given by equation (1). In the equation (1), the coefficient “2” is a pair (two) of γ when one positron is annihilated.
α = 2NABC (1)
It means that a line is emitted. The probability W that one detection element detects γ-rays within the irradiation time T is given by equation (2). So as to reduce the value of W in equation (2)
W = 1−exp (−Tα) (2)
By determining the irradiation time T, the influence of γ-rays incident on one radiation detector during an X-ray CT inspection can be ignored.
An example of the X-ray irradiation time T will be described below. The specific X-ray irradiation time T was determined based on the equations (1) and (2). In a PET test, the intensity of radiation in the body caused by the PET drug to be administered to the subject is about 370 MBq at the maximum (N = 370 MBq), and the in-vivo rate A of γ-rays passes through the body of the subject within a radius of 15 cm. Assuming water, it is about 0.6 (A = 0.6). For example, when a radiation detector having a side of 5 mm is arranged in a ring shape with a radius of 50 cm, the incidence rate B obtained from the solid angle of one radiation detector is 8 × 10 -6 (B = 8 × 10 -6 ). The detection sensitivity C of the radiation detector is about 0.6 (C = 0.6) at the maximum when a semiconductor radiation detector is used. From these values, the detection rate α of one radiation detector for γ-rays is about 2000 (pieces / sec). If the X-ray irradiation time T is, for example, 1.5 μsec, the probability W that one radiation detector detects γ-rays during X-ray detection is 0.003, and the γ-rays can be almost ignored. When the radioactivity to be administered in the body is 360 MBq or less, if the X-ray irradiation time is 1.5 μsec or less, W <0.003, that is, the detection probability of γ-ray is 0.3% or less and can be ignored.
An X-ray CT inspection and a PET inspection in the present embodiment using the imaging apparatus 2B to which the above principle is applied will be specifically described.
An X-ray CT inspection and a PET inspection in the present embodiment will be described. The PET drug is previously administered to the subject 42 as a subject by injection or the like so that the radioactivity for intracorporeal administration becomes 370 MBq. Thereafter, the examinee 42 waits for a predetermined time until the PET drug diffuses into the body of the examinee 42 and gathers in the affected part (for example, an affected part of cancer) to be ready for imaging. The PET drug is selected according to the diseased part to be examined. After the elapse of the predetermined time, the bed 20 on which the examinee 42 is lying is inserted into the hole 41 of the imaging device 2 together with the examinee 42. The X-ray CT inspection and the PET inspection are performed using the imaging device 2. The examinee 42 to which the PET drug was administered was inserted into the hole 41, and a voltage was applied from the power supply 50 to each radiation detector 5, and then each radiation detector 5 was released from the examinee 42. Detects gamma rays. That is,
PET inspection is started. After the PET inspection is started, the X-ray CT inspection is started.
The X-ray CT inspection will be described. When starting the X-ray CT examination, the driving device control device 21 outputs a driving start signal, and a switch connected to a power supply connected to the motor of the X-ray source driving device 15 (hereinafter, referred to as a motor switch). Close. The rotational force of the motor is transmitted to the pinion via the speed reduction mechanism, and the X-ray source device 14, that is, the X-ray source 17 moves in the circumferential direction along the guide rail 12. The X-ray source 17 moves around the examinee 42 at a set speed while being inserted into the hole 41. At the end of the X-ray CT examination, the drive controller 21 outputs a drive stop signal to open the motor switch. Thereby, the movement of the X-ray source 17 in the circumferential direction is stopped. In the present embodiment, all the radiation detectors 5 do not move in the circumferential direction and do not move in the axial direction of the hole 41. The drive controller 21 and the X-ray source controller 22 are installed on the detector support member 8. The transmission of the control signal from the driving device control device 21 and the X-ray source control device 22 to the moving X-ray source device 14 employs a known technique that does not hinder the movement of the X-ray source device 14.
The X-ray source control device 22 controls the emission time of X-rays from the X-ray source 17. That is, the source control device 22 repeatedly outputs the X-ray generation signal and the X-ray stop signal. The output of the first X-ray generation signal is performed based on the input of the drive start signal to the X-ray source control device 22. A switch provided between the anode (or cathode) of the X-ray tube and the power supply in the X-ray source 17 (hereinafter, referred to as an X-ray source switch, not shown) is closed by the output of the X-ray generation signal, When the first set time has elapsed, an X-ray stop signal is output to open the X-ray source switch, and when the second set time has elapsed, the X-ray source switch is closed. A voltage is applied between the anode and the cathode for a first set time, and no voltage is applied for a second set time. Under the control of the X-ray source control device 22, X-rays of 80 keV are emitted in a pulse form from the X-ray tube. The irradiation time T, which is the first set time, is set to, for example, 1 μsec so that the detection probability of γ-rays in the radiation detector 5 can be ignored. The second set time is a time T0 during which the X-ray source 17 moves between one radiation detector 5 and another radiation detector 5 adjacent to the radiation detector 5 in the circumferential direction. It is determined by the moving speed of the source 17. The first and second set times are stored in the X-ray source control device 22.
By repeatedly outputting the X-ray stop signal and the X-ray generation signal, the X-ray source 17 emits X-rays during the first set time, that is, 1 μsec, and stops emitting X-rays during the second set time. . The emission and stop of the X-rays are repeated during the period in which the X-ray source 17 moves in the circumferential direction.
The X-ray 57 emitted from the X-ray source 17 is applied to the examinee 42 in a fan beam shape. As the X-ray source 17 moves in the circumferential direction, the examinee 42 is irradiated with X-rays 57 from the surroundings. X-rays transmitted through the examinee 42 (for example, X-rays transmitted through the affected part 56) 57 are arranged around the radiation detector 5 at a position 180 degrees from the X-ray source 17 with respect to the axis of the hole 41. It is detected by a plurality of radiation detectors 5 located in the directions. These radiation detectors 5 output detection signals of the X-rays 57. This X-ray detection signal is input to the corresponding signal discriminating device 27 via the corresponding wiring 49. Those radiation detectors 5 detecting the X-rays are referred to as first radiation detectors 4 for convenience.
511 keV γ-rays 58 due to the PET drug are emitted from the affected part (cancer part) 56 of the examinee 42 on the bed 16. Radiation detectors 5 other than the first radiation detector 5 detect γ-rays 58 and output γ-ray detection signals. The radiation detector 5 that detects γ-rays is referred to as a second radiation detector 5 for convenience. Among the second radiation detectors 5, the γ-ray detection signal output from the second radiation detector 5 located on the first layer is input to the corresponding signal discriminating device 27 via the corresponding wiring 49, and The γ-ray detection signal output from the second radiation detector 5 located in the third layer is input to the corresponding γ-ray discriminating device 32 via the wiring 54. Only the radiation detector 5 arranged on the first layer is connected to the signal discriminating device 61 having the X-ray signal processing device 33. This is because most (90% or more) of the X-rays transmitted through the examinee 42 are detected by the first radiation detector 5 because the energy of the X-rays is 80 keV.
In the signal discriminator 27, the γ-ray detection signal output from the second radiation detector 5 in the first layer is transmitted to the γ-ray discriminator 32, and the X-ray detection signal output from the first radiation detector 5 is X-ray. The signal is transmitted to the line signal processing device 33. Such transmission of each detection signal is performed by a switching operation of the changeover switch 28 of the signal discrimination device 27. The switching operation of connecting the movable terminal 29 of the changeover switch 28 to the fixed terminal 30 or the fixed terminal 31 is performed based on a switching control signal output from the driving device control device 21. At the time of the X-ray CT inspection, the driving device control device 22 selects the first radiation detector 5 among the radiation detection devices 5 in the first layer, and operates the signal discrimination device 27 connected to the first radiation detector 5 in the movable state. Terminal 29 is connected to fixed terminal 31.
The selection of the first radiation detector 5 will be described. An encoder (not shown) is connected to a motor in the X-ray source driving device 15. The driving device control device 22 receives the detection signal of the encoder and obtains the position of the X-ray source driving device 15, that is, the X-ray source 17 in the circumferential direction of the detector support member 8 (the hole 41). The radiation detector 5 located 180 ° opposite to the position 17 is selected using the stored data of the position of each radiation detector 5. Since the X-ray 57 emitted from the X-ray source 17 has a width in the circumferential direction of the guide rail 12, the radiation detector 5 that detects the X-ray 57 transmitted through the examinee 42 is selected. In addition to the radiation detector 5, a plurality of radiation detectors exist in the circumferential direction. The drive controller 22 also selects the plurality of radiation detectors 5. These radiation detectors 5 are first radiation detectors 5. As the X-ray source 17 moves in the circumferential direction, the first radiation detector 5 also changes. As the X-ray source 17 moves in the circumferential direction, the first radiation detector 5 also appears to move in the circumferential direction in a pseudo manner. When the drive controller 22 selects another radiation detector 5 in accordance with the movement of the X-ray source 17 in the circumferential direction, the movable controller connected to the radiation detector 5 which is newly the first radiation detector 5 Terminal 29 is connected to fixed terminal 31. The movable terminal 29 connected to the radiation detector 5 which is no longer the first radiation detector 5 as the X-ray source 17 moves in the circumferential direction is connected to the fixed terminal 30 by the drive controller 22. Depending on the position of the X-ray source 17, the individual radiation detectors 5 in the first layer sometimes become the first radiation detectors 5, and become the second radiation detectors 5 in other cases. Therefore, one radiation detector 5 of the first layer outputs both the X-ray detection signal and the γ-ray detection signal with a time lag.
The first radiation detector 5 detects X-rays emitted from the X-ray source 17 and transmitted through the examinee 42 during the first set time of 1 μsec. As described above, the probability that the first radiation detector 5 detects γ-rays emitted from the subject 42 during 1 μsec is negligibly small. A large number of γ-rays 58 generated in the affected area 56 of the subject 42 due to the PET agent are emitted not in a specific direction but in all directions. As described above, these γ-rays 58 are emitted in pairs in substantially opposite directions (180 ° ± 0.6 °), and are detected by any of the second radiation detectors 5.
The signal processing of the signal discrimination device 27 when the X-ray detection signal and the γ-ray detection signal output from the first radiation detector 5 are input will be described. The X-ray detection signal output from the first radiation detector 5 is input to the X-ray signal processing device 33 as described above. The X-ray signal processing device 33 integrates the input X-ray detection signal by an integrator, and outputs an integrated value of the X-ray detection signal, that is, information on the measured X-ray intensity. The intensity information of the X-ray detection signal is transmitted to the computer 36 via the wiring 53 and stored in the storage device 37.
The γ-ray detection signal output from the second radiation detector 5 of the first layer is input to the γ-ray discrimination device 32 by the operation of the changeover switch 28. The energy of the γ-ray emitted from the diseased part 56 due to the disappearance of the positron emitted from the PET drug is 511 keV. However, when γ-rays are scattered in the body of the subject 42, the energy is lower than 511 keV. The γ-ray discriminating device 32 removes scattered γ-rays, for example, using 400 keV whose energy is lower than 511 keV as an energy set value, and a filter (not shown) that passes a γ-ray detection signal having energy equal to or more than this energy set value. ). This filter receives the γ-ray detection signal output from the fixed terminal 30. Here, as an example, the reason why the energy setting value is set to 400 keV is because the dispersion of the γ-ray detection signal generated when 511 keV γ-rays enter the radiation detector 5 is considered. The γ-ray discrimination device 32 generates a pulse signal having a predetermined energy when a γ-ray detection signal having an energy equal to or more than an energy set value (400 keV) is input. The γ-ray discrimination device 32 is a γ-ray detection signal processing device, and adds time information and position information indicating the position of the radiation detector 5 connected to the γ-ray discrimination device 32 to the output pulse signal. The time information is one of the time when the γ-ray detection signal is input to the γ-ray discrimination device 32 and the time when the pulse signal is output from the γ-ray discrimination device 32.
The second and third radiation detectors 5 are all second radiation detectors. The γ-ray discriminating device 32 connected to the second-layer and third-layer radiation detectors 5 by the wiring 54 also has the same function as the γ-ray discriminating device 32 in the signal discriminating device 27 described above.
The coincidence counting device 34 receives the pulse signals output from all the γ-ray discriminating devices 32. The coincidence device 34 detects two γ-rays 58 of each pair of γ-rays (about 180 ° around the axis of the hole 30 (strictly speaking, 180 ± 0.6 °). ) Simultaneous counting is performed using each pulse signal for each γ-ray detection signal output from a pair of second radiation detectors 5 present at different positions, and the count value for those γ-ray detection signals ( γ-ray counting information). The coincidence counting device 34 determines whether each pulse signal corresponds to the detection signal of each γ-ray of the γ-ray pair based on each time information given to the pulse signal. That is, if the difference between the two pieces of time information is within a set time (for example, 10 nsec), it is determined that the pulse signal is a pulse signal for a pair of γ-rays 58 generated by the disappearance of one proton. Further, the coincidence counting device 34 converts each position information given to those pulse signals into data as each position of the corresponding pair of second radiation detectors 5, that is, position information of each γ-ray detection point. The coincidence counting device 34 outputs the above-described count value information for each of the γ-ray detection signals and the position information of the two detection points where the paired γ-rays are detected. The count value and the position information are transmitted to the computer 36 and stored in the storage device 37.
The computer 36 executes processing based on the processing procedure of steps 60 to 65 shown in FIG. The computer 36 executing such a process creates first tomographic image information using the first information (specifically, γ-ray counting information and position information of γ-ray detection points), and generates the second information (specifically, Specifically, X-ray intensity information and X-ray detection position information) are used to generate second tomographic image information (specifically, X-ray CT image data), and the first tomographic image information and the second tomographic image information are used. A tomographic image creating unit that creates third tomographic image information (specifically, combined tomographic image data) including the tomographic image information. Count value information of the γ-ray detection signal counted by the coincidence counting device 34, position information of the γ-ray detection point output from the coincidence counting device 34, X-ray intensity information output from the X-ray signal processing device 33, and X X-ray detection position information given to the line intensity is input (step 60). The input count value information of the γ-ray detection signal, the position information of the γ-ray detection point, the X-ray intensity information, and the X-ray detection position information are stored in the storage device 37 (step 61).
Using the X-ray intensity information and the X-ray detection position information, a tomographic image of a cross section of the examinee 42 (hereinafter, the cross section refers to a cross section in a state where the examinee stands) is reconstructed ( Step 62). The reconstructed tomographic image is called an X-ray CT image. A specific process for reconstructing this tomographic image will be described. First, the X-ray attenuation rate of each voxel in the body of the subject 42 is calculated using the X-ray intensity information. This attenuation rate is stored in the storage device 37. In order to reconstruct the X-ray CT image, the position of the X-ray source 17 and the position of the radiation detector 5 that has detected the X-ray (X (Obtained from the line detection position information) to obtain a line attenuation coefficient in the body of the subject 42 to be examined. The position of the X-ray source 17 at the time of movement detected by the encoder is added to the X-ray intensity information by each X-ray signal processing device 33 and transmitted to the computer 36. The CT value at each voxel is calculated based on the value of the linear attenuation coefficient at each voxel, which is obtained by the filtered back projection method using the linear attenuation coefficient. The data of the X-ray CT image is obtained using those CT values, and is stored in the storage device 37. In step 62, an X-ray CT image in a cross section passing through the affected area where the PET drug is accumulated is also reconstructed.
A tomographic image of the cross section of the examinee 42 including the affected part (for example, the affected part of cancer) is reconstructed using the count value of the γ-ray detection signal at the corresponding position (step 63). A tomographic image reconstructed using the count value of the γ-ray detection signal is called a PET image. This processing will be described in detail. Using the count value of the γ-ray detection signal read from the storage device 37, the pair of second radiation detectors 5 (specified from the position information of the γ-ray detection point) that have detected γ-rays generated by the positron annihilation The number of γ-ray pairs generated in the body between the semiconductor element portions (the number of γ-ray pairs generated in response to the disappearance of a plurality of positrons) is determined. Using the number of γ-ray pairs generated, the γ-ray pair generation density in each voxel is determined by the filtered back projection method. PET image data can be obtained based on these γ-ray pair generation densities. The data of the PET image is stored in the storage device 37.
The PET image data and the X-ray CT image data are combined to obtain combined tomographic image data including both data, and stored in the storage device 37 (step 64). The PET image data at the position of the affected part and the X-ray CT image data at the position are combined to obtain combined tomographic image data of the cross section of the examinee 42 at the position of the affected part. The combination of the PET image data and the X-ray CT image data can be easily and accurately performed by adjusting the position of the center axis of the hole 41 in both image data. That is, since the data of the PET image and the data of the X-ray CT image are created based on the detection signal output from the shared radiation detector 5, the positioning can be performed with high precision as described above. The data of the composite tomographic image is called from the storage device 37, output to the display device 38 (step 65), and displayed on the display device 38. Since the synthetic tomographic image displayed on the display device 38 includes the X-ray CT image, the position of the affected part in the PET image in the body of the examinee 42 can be easily confirmed. That is, since the X-ray CT image includes an image of the internal organs and bones, the doctor can specify the position where the affected part (for example, the affected part of cancer) is present in relation to the internal organs and bones.
In the radiation inspection apparatus 1, a plurality of radiation detectors 5 are stacked and arranged in the radial direction of the hole 41 (FIGS. 1 to 4). For example, as shown in FIG. 9A, two γ-rays 58a and 58b emitted from the γ-ray pair generation point 70 (in the affected part 56) in the body of the subject 42 enter the radiation detectors 5f and 5g. Consider the case. Since it is not known at which position in the radiation detector the γ-ray has attenuated, in the conventional method, a line connecting the tip positions of the pair of radiation detectors 5f and 5h, that is, a line 71 shown in FIG. did. However, in the radiation inspection apparatus 1, since the radiation detectors 5 are stacked in the radial direction of the hole 41, a γ-ray detection signal of the radiation detector 5g located outside in the radial direction is obtained, and the radiation detection is performed. The line 72 connecting the detector 5f and the radiation detector 5g can be a detection line. That is, it is possible to grasp the attenuation position in the depth direction of the radiation detector 5, which was not known in the conventional example. As a result, the detection line 72 accurately passes through the position where the pair of γ-rays is generated, so that the accuracy of the image is improved. As a result, the detection line is closer to the actual γ-ray pair generation point, and the accuracy of the measurement data is improved.
In the present embodiment, since the radiation detection device 43 is composed of a plurality of radiation detectors 5 that output both an X-ray detection signal and a γ-ray detection signal, the radiation detection device 43 is a γ-ray detection unit and It is also a detection unit. That is, the radiation detection device 43 has both functions of a γ-ray detection unit and an X-ray detection unit. In the present embodiment, the X-ray detection unit is located in a region formed between one end of the γ-ray detection unit and the other end of the γ-ray detection unit in the longitudinal direction of the bed 20. The radiation detection device 43 is an X-ray detection unit that detects an X-ray 57 emitted from the X-ray source 17 and transmits through the subject 42 and outputs a detection signal of the X-ray 57. At the position of the examinee 42 who is irradiating the X-ray 57, a γ-ray 58 emitted from the portion of the examinee 42 through which the X-ray 57 penetrates (the affected part 56) due to the PET drug is detected. It is a γ-ray detector that outputs 58 detection signals.
(1) In the present embodiment, since a plurality of detector units 4 are attached to the detector support member 8 via the connector section, these detector units 4, specifically, a large number of radiation detectors 5 need to be attached. Can be done in a short time. Therefore, the manufacturing time of the imaging device 2, that is, the radiation inspection device 1 can be reduced.
(2) Since the detector unit 4 is detachably attached to the detector support member 8 via the connector, when the radiation detector 5 fails, the detector unit 4 including the failed radiation detector 5 is detected by the detector. It can be easily removed from the support member 8. Further, the new detector unit 4 can be easily attached to the detector support member 8 at the position of the detector unit from which the detector unit has been removed. As described above, according to the present embodiment, the failed radiation detector 5 can be easily replaced.
(3) In this embodiment, a plurality of radiation detectors 5 are arranged not only in the axial direction and the circumferential direction of the hole 41 (detector support member 8) but also in the radial direction, so that the radiation detectors 5 are used in the conventional PET inspection. It is possible to obtain a γ-ray detection signal at a position subdivided in the radial direction of the hole 41 without reducing the signal transmission material unlike a radiation detector to be used. For this reason, in the present embodiment, it is possible to obtain accurate position information (position information of the radiation detector 5 that has output the γ-ray detection signal) at which the γ-ray has reached in the radial direction of the hole 41. In the conventional PET inspection, one radiation detector is arranged in the radial direction of the hole 41, and a reflection material is arranged inside the radiation detector so that the signal transmitting substance reaches the photomultiplier according to the pattern. The information of the position where the γ-ray has reached in the radial direction of the hole 41 has been obtained. At this time, a part of the signal transmitting substance is attenuated in the radiation detector or reflected outside the radiation detector due to the reflecting material, so that the signal transmitting substance is reduced and the energy resolution is reduced.
(4) In the present embodiment, since a plurality of independent radiation detectors 5 are arranged in the radial direction of the hole 41, all of the signal transmitting substances of the respective radiation detectors 5 can be used for detecting γ-rays. The energy resolution of the radiation detector 5 is improved. When the radiation detector 5 having high energy resolution is used in the PET inspection, it is possible to distinguish between γ-rays whose energy has been attenuated by scattering and γ-rays of 511 keV energy which are not scattered. As a result, more scattered radiation can be removed by the filter of the γ-ray discriminating device 32.
(5) In this embodiment, the holes can be formed without reducing the number of signal transmitting substances in the radiation detector.
Since it is possible to acquire the information of the accurate arrival position of the γ-ray in the radial direction of 31, it is possible to improve the accuracy of the tomographic image by using the information of the accurate arrival position of the γ-ray, and it is not necessary to use the reflector of the radiation detector This has made it possible to prevent a decrease in signal transmitting substances, improve energy resolution, and suppress the influence of scattered radiation on tomographic image reconstruction. As a result, the present embodiment can improve the accuracy of the tomographic image, that is, the diagnostic accuracy of the PET examination.
(6) In the present embodiment, since the semiconductor radiation detector is used as the radiation detector 5, a plurality of radiation detectors 5 can be arranged in the radial direction of the hole 41, and thus a plurality of radiation detections can be performed. Even if the device 5 is arranged, the imaging device 2 does not become large.
(7) In the present embodiment, since the radiation detector 5 is a semiconductor radiation detector, a photomultiplier tube is not required as compared with a radiation detector using a scintillator, and the imaging device 2 can be downsized. it can.
(8) According to the present embodiment, it is possible to arrange the radiation detectors 5 densely by disposing the radiation detectors 5 which are semiconductor radiation detectors on the support substrate. In particular, since the radiation detectors 5 with a small detector width can be densely arranged in the circumferential direction of the hole 41, the resolution of the tomographic image can be increased (small image voxel size).
(9) According to the present embodiment, the radiation detectors 5 can be arranged densely by arranging the radiation detectors 5 on the support substrate 6. In particular, a plurality of radiation detectors 5 can be arranged in the radial direction of the hole 41, and high detection efficiency can be achieved. Furthermore, since each radiation detector 5 in the radial direction can independently detect γ-rays, the resolution in the radial direction is improved. In particular, in a 3D (three-dimensional) -PET inspection, γ-rays may be incident on the radiation detector 5 obliquely, but the resolution in the radial direction is improved to more accurately detect the γ-ray incident direction. be able to. Therefore, it is possible to improve the quality of the obtained PET image.
(10) According to the present embodiment, in order to arrange the wiring connected to the radiation detector 5 in the support substrate 6, the interval between the radiation detectors 5 in the circumferential direction of the hole 41 and the axial direction thereof is reduced. it can. Shortening the interval between the radiation detectors 5 reduces the leakage of detection of γ-rays between the radiation detectors 5 and substantially increases the efficiency of γ-ray detection. By substantially increasing the detection efficiency of γ-rays, the PET inspection time can be reduced.
(11) Since the radiation detector 5 that detects γ-rays is used as the radiation detector 5 that detects X-rays, the radiation inspection apparatus 1 includes the radiation detector 5 that detects X-rays and the radiation detection that detects γ-rays. It is not necessary to separately provide the device 5 and the configuration can be simplified and the size can be reduced. The radiation detector 5 outputs both an X-ray detection signal and a γ-ray detection signal.
(12) In the present embodiment, since the X-ray detection unit is located in a region formed between one end of the γ-ray detection unit and the other end of the γ-ray detection unit in the longitudinal direction of the bed 20, Even if the examinee 42 moves during the examination without moving the bed 20, the first tomographic image created based on the first information obtained from the γ-ray detection signal output from the γ-ray detection unit (PET image) and a second tomographic image (X-ray CT image) obtained from the X-ray detection signal output from the X-ray detection unit are combined to create a tomographic image of the examinee 42. The accuracy of the image can be improved. This makes it possible to improve the diagnostic accuracy for the subject by using the tomographic image. Specifically, the position and size of the affected part of the cancer can be accurately recognized. In particular, cancer of the lymph gland, which is a small organ, can be accurately diagnosed.
(13) In the present embodiment, as described above, the radiation detection device 43 includes a plurality of radiation detectors 5 (X-ray detection that obtains X-ray detection signals) that output both X-ray detection signals and γ-ray detection signals. Is performed using the radiation detector 5 that detects a γ-ray that obtains a γ-ray detection signal), and thus has both functions of a γ-ray detection unit and an X-ray detection unit. It can be said that the radiation detection device 43 has a γ-ray detection unit and an X-ray detection unit arranged coaxially. For this reason, the present embodiment uses the X-ray detection signal, which is one output signal of the radiation detector 5 arranged in the circumferential direction of the detector support member 8, to image the internal organs and bones of the examinee 42. The first tomographic image can be reconstructed at the position of the affected part (the PET drug is accumulated), and the affected part of the subject 42 using the γ-ray detection signal which is another output signal of the radiation detector 5 The second tomographic image including the image can be reconstructed. Since the data of the first tomographic image and the data of the second tomographic image are reconstructed based on the output signal of the radiation detector 5 for detecting both the transmitted X-ray and the γ-ray, the first tomographic image at the position of the diseased part And the data of the second tomographic image can be accurately aligned and combined. Therefore, a high-accuracy tomographic image (synthetic tomographic image) including images of the affected part, internal organs, bones, and the like can be easily obtained. According to this composite tomographic image, the position of the affected part can be accurately known in relation to the internal organs and bones. For example, by aligning the data of the first tomographic image and the data of the second tomographic image based on the axis of the detector support member 8 (or the hole 41) of the imaging device 2, the two tomographic images can be easily synthesized. Image data can be obtained.
(14) In the present embodiment, the X-ray detection unit detects X-rays 57 emitted from the X-ray source 17 and transmitted through the affected part 56 of the examinee 42, and the examinee 42 irradiating the X-rays In order to detect the γ-ray emitted from the site (affected part) through which the X-rays in the body of the examinee 42 penetrate at the position of the examinee due to the radiopharmaceutical by the γ-ray detector, the examinee 42 is moved by the bed 20. X-ray CT inspection and PET inspection can be performed at the same position without moving. During the two examinations, the X-ray detector outputs a detection signal of X-rays transmitted through the affected part 56 of the examinee 42, and the γ-ray detector outputs a detection signal of γ-ray emitted from the affected part 56. To combine the first tomographic image data at the position of the affected part 56 obtained based on the X-ray detection signal and the second tomographic image data at the position of the affected part obtained based on the γ-ray detection signal, Even when the examinee 42 moves on the bed 20 without being able to endure during the examination, the tomographic image data can be accurately synthesized. That is, highly accurate synthesized tomographic image data can be obtained. Therefore, by using the combined tomographic image data (synthesized tomographic image) at the position of the diseased part 56 displayed on the display device 38, the diagnostic accuracy of the diseased part 52 can be improved. In particular, even when an affected part is present in a place where an organ is complicated, the position of the affected part can be appropriately grasped by the synthesized tomographic image obtained in the present embodiment, and the diagnostic accuracy of the affected part is improved.
(15) In the present embodiment, the X-ray source 17 can be moved in the axial direction of the radiation detection unit 65 during the radiological examination period by using the X-ray source axial movement device (for example, the axial movement arm 16). Without moving the examiner 42 in the axial direction of the radiation detection device 43, the X-ray CT inspection can be performed on the inspection target range while performing the PET inspection on the inspection target range. When the X-ray CT examination for the examination target area is performed by moving the examinee 42 by moving the bed 20 without moving the X-ray source 17 in the axial direction, the position of the PET drug accumulation part Move in the axial direction. This means that the position at which the γ-ray pair is generated is moved in the axial direction, so that noise in the generation of the PET image data increases, and it becomes impossible to obtain highly accurate PET image data. In the present embodiment, since the position at which the γ-ray pair is generated does not move in the axial direction, highly accurate PET image data is obtained, and the accuracy of the combined tomographic image data is also improved.
(16) In the present embodiment, the radiation detectors 5 included in the radiation detection device 43 can detect a plurality of pairs of γ-rays emitted from the subject 42 and move in the circumferential direction. X-rays emitted from the X-ray detector 17 and transmitted through the examinee 42 can also be detected. For this reason, the prior art required an imaging device for detecting X-rays and another imaging device for detecting γ-rays as an imaging device, but the present embodiment employs a single imaging device for detecting X-rays and γ-rays. And the configuration of the radiation inspection apparatus capable of performing both the X-ray CT inspection and the PET inspection can be simplified.
(17) In the present embodiment, the X-ray detection signal necessary for creating the first tomographic image and the γ-ray detection signal necessary for creating the second tomographic image are shared by the radiation detector 5. Therefore, the time required for the examination of the examinee 42 (examination time) can be significantly reduced. In other words, an X-ray detection signal required to generate the first tomographic image and a γ-ray detection signal required to generate the second tomographic image can be obtained in a short inspection time. In the present embodiment, unlike the related art, it is not necessary to move the examinee 42 from an imaging device that detects transmitted X-rays to another imaging device that detects γ-rays. Further contributes to shortening
(18) In the present embodiment, since the X-ray source 17 is rotated and the radiation detection device 43 is not moved in the circumferential direction and the axial direction of the hole 41, the X-ray source is moved more than the motor required to move the radiation detection device 43. The capacity of the motor that rotates the radiation source 17 can be reduced. The power consumption required for driving the latter motor can also be made smaller than that of the former motor.
(19) Since the γ-ray detection signal input to the X-ray signal processing device 33, that is, the first signal processing device, is significantly reduced, highly accurate data of the first tomographic image can be obtained. For this reason, by using the image data obtained by combining the data of the first tomographic image and the data of the second tomographic image, the position of the affected part can be known more accurately.
(20) In this embodiment, since the X-ray source 17 circulates inside the radiation detection device 43, the inner diameter of the detector support member 8 increases, and radiation detection can be installed in the circumferential direction inside the detector support member 8. The number of vessels 5 can be increased. Increasing the number of radiation detectors 5 in the circumferential direction improves sensitivity and resolution, and improves resolution of a tomographic image in a cross section of the examinee 42.
(21) In the present embodiment, since the axial movement arm 16 and the X-ray source 17 are located inside the radiation detecting device 434, they are emitted from the subject 42 during the X-ray CT examination. , The radiation detector 5 located immediately behind them cannot detect the γ-rays, and there is a possibility that the detection data necessary for creating a PET image is lost. However, in the present embodiment, as described above, since the X-ray source 17 and the axial movement arm 16 are circulated in the circumferential direction by the X-ray source driving device 15, data loss does not substantially matter. . In particular, the orbiting speed of the X-ray source 17 and the axial movement arm 16 is about 1 second / 1 slice, which is sufficiently short as compared with the time required for PET inspection on the order of several minutes at the shortest. Even in this case, the loss of the data does not substantially matter. Further, when the X-ray CT inspection is not performed and the PET inspection is performed, the X-ray source 17 and the axial movement arm 16 detect the γ-ray because the X-ray source 17 is housed in the X-ray source driving device 15. Does not hinder.
Further, the inspection time required to obtain an X-ray detection signal required to generate an X-ray CT image is shorter than the inspection time required to obtain a γ image signal required to generate a PET image. Therefore, during the examination time for obtaining the γ-ray detection signal, the X-ray source 17 constantly irradiates the X-ray to the examinee 42 to obtain the X-ray detection signal, so that the examinee 42 Even in the case of moving, the deviation of the data of the PET image due to the swing of the examinee 42 can be corrected from the continuous image of the X-ray CT images obtained based on the X-ray detection signal.
Although the wiring connected to the radiation detector 5 is arranged in the support substrate 6, a through hole is formed in the support substrate 6, and the wiring is passed through the through hole from the surface of the support substrate 6 on which the radiation detector 5 is installed. The wiring may be provided on the opposite side of the support substrate 6 on which the radiation detector 5 is not provided, by being drawn out to the opposite side by a through-hole provided on the opposite side. In that case, a groove may be formed on the surface of the support substrate 6 on the side where the radiation detector 5 is not installed, and wiring may be installed in the groove. Further, a multilayer wiring board may be used as a support substrate, and wiring may be provided in the multilayer wiring board. Further, by using the multilayer wiring board, the radiation detectors 5 can be arranged on both sides of the multilayer wiring board.
A radiation inspection apparatus according to a second embodiment which is another embodiment of the present invention will be described below. The radiation inspection apparatus of the present embodiment differs from the radiation inspection apparatus 1 of the first embodiment only in the configuration of the detector unit. A detector unit 4A used in this embodiment, which has a different configuration from the detector unit 4 used in the first embodiment, will be described with reference to FIGS.
In the detector unit 4A, a plurality (for example, nine) of radiation detectors 5D are installed on one surface of the support substrate 6 in three rows and three columns. Each radiation detector 5D is the same semiconductor radiation detector as the radiation detector 5, and is arranged in three layers in the radial direction of the detector support member 8. In one row of the detector support member 8 arranged in the radial direction, the radiation detector 5A 1 , Radiation detector 5B in the second layer 1 And the third layer radiation detector 5C 1 Are respectively arranged.
Radiation detector 5A 1 Has five detection elements, namely, detection elements 74A, 74B, 74C, 74D, and 74E. The detection elements 74A, 74B, 74C, 74D, 74E are arranged in that order from the inside in the radial direction of the detector support member 8. The detection element 74A is disposed at the innermost position, and the detection element 74E is disposed at the outermost position. A cathode electrode 77A is provided on the inner surface of the detection element 74A. The detection element 74A and the detection element 74B are adjacent to each other with an anode electrode 78A provided on the outer surface of the detection element 74A and the inner surface of the detection element 74B interposed therebetween. The detecting element 74B and the detecting element 74C are adjacent to each other with a cathode electrode 77B provided on the outer surface of the detecting element 74B and the inner surface of the detecting element 74C interposed therebetween. The detection element 74C and the detection element 74D are adjacent to each other with an anode electrode 78B provided on the outer surface of the detection element 74C and the inner surface of the detection element 74D interposed therebetween. The detection element 74D and the detection element 74E are adjacent to each other with a cathode electrode 77C provided on the outer surface of the detection element 74D and the inner surface of the detection element 74E therebetween. An anode electrode 78C is provided on the outer surface of the detection element 74E.
Radiation detector 5B 1 Has five detection elements, namely, detection elements 75A, 75B, 75C, 75D, and 75E. The detection elements 75A, 75B, 75C, 75D, and 75E are arranged in that order from the inside in the radial direction of the detector support member 8. The detection element 75A is disposed at the innermost position, and the detection element 75E is disposed at the outermost position. A cathode electrode 79A is provided on the inner surface of the detection element 75A. The detection element 75A and the detection element 75B are adjacent to each other with an anode electrode 80A provided on the outer surface of the detection element 75A and the inner surface of the detection element 75B interposed therebetween. The detection element 75B and the detection element 75C are adjacent to each other with a cathode electrode 79B provided on the outer surface of the detection element 75B and the inner surface of the detection element 75C interposed therebetween. The detection element 75C and the detection element 75D are adjacent to each other with the anode electrode 80B provided on the outer surface of the detection element 75C and the inner surface of the detection element 75D interposed therebetween. The detection element 75D and the detection element 75E are adjacent to each other with a cathode electrode 79C provided on the outer surface of the detection element 75D and the inner surface of the detection element 75E interposed therebetween. An anode electrode 80C is provided on the outer surface of the detection element 75E.
Radiation detector 5C 1 Has five detection elements, namely, detection elements 76A, 76B, 76C, 76D, and 76E. The detection elements 76A, 76B, 76C, 76D, 76E are arranged in that order from the inside in the radial direction of the detector support member 8. The detection element 76A is disposed at the innermost position, and the detection element 76E is disposed at the outermost position. A cathode electrode 81A is provided on the inner surface of the detection element 76A. The detection element 76A and the detection element 76B are adjacent to each other with the anode electrode 82A provided on the outer surface of the detection element 76A and the inner surface of the detection element 76B interposed therebetween. The detection element 76B and the detection element 76C are adjacent to each other with a cathode electrode 81B provided on the outer surface of the detection element 76B and the inner surface of the detection element 76C interposed therebetween. The detection element 76C and the detection element 76D are adjacent to each other with the anode electrode 82B provided on the outer surface of the detection element 76C and the inner surface of the detection element 76D interposed therebetween. The detection element 76D and the detection element 76E are adjacent to each other with a cathode electrode 81C provided on the outer surface of the detection element 76D and the inner surface of the detection element 76E interposed therebetween. An anode electrode 82C is provided on the outer surface of the detection element 76E.
The ground wire 45 is connected to the cathode electrodes 77A, 77B, 77C, 79A, 79B, 79C, 81A, 81B, 81C. The wiring 74 is connected to the anode electrodes 78A, 78B, 78C. Wiring 75 is connected to anode electrodes 80A, 80B, 80C. Wiring 76 is connected to anode electrodes 82A, 82B, 82C. The ground wire 45 is connected to the connector terminal 7D of the connector section 7. The wiring 74 is connected to the connector terminal 7A of the connector unit 7. The wiring 75 is connected to the connector terminal 7B of the connector section 7. The wiring 76 is connected to the connector terminal 7C of the connector unit 7. Each of the radiation detectors 5D included in the other two rows is also connected to another connector terminal provided on the connector unit 7 in the same manner. The ground wire 45 and the wirings 74, 75, 76 are all installed in the support substrate 6. The large number of detector units 4A are mounted and held on the detector support unit 23 by fitting the connector terminals such as the connector terminals 7A provided on the respective connector units 11 provided on the detector support unit 23. You. Similarly to the detector unit 4, the detector units 4A also surround the hole 41 and are arranged in a large number in the circumferential direction and the axial direction of the hole 41.
Radiation detector 5A 1 , 5B 1 , 5C 1 Has three or more detection elements having at least two surfaces, that is, semiconductor elements, and alternately arranges an anode electrode and a cathode electrode between different semiconductor elements. Radiation detector 5A 1 This will be specifically described with reference to FIG. Radiation detector 5A 1 Are detected between different detection elements, that is, between the detection element 74A and the detection element 74B, between the detection element 74B and the detection element 74C, between the detection element 74C and the detection element 74D, and between the detection element 74D and the detection element 74EC. An anode electrode and a cathode electrode are alternately arranged between them, such as an anode electrode 78A between the detection elements 74A and 74B and a cathode electrode 77B between the detection elements 74B and 74C.
By fitting the connector portion 7 into the connector portion 11, the first three radiation detectors 5A 1 Are separately connected to three signal discrimination devices 27 in the signal discrimination unit 25. Also, three radiation detectors 5B of the second layer 1 And three radiation detectors 5C of the third layer 1 Are separately connected to six γ-ray discriminating devices 32 provided in the signal discriminating unit 25 other than the signal discriminating device 27.
The radiation inspection apparatus of the present embodiment incorporating the detector unit 4A can obtain the effects (1) to (21) produced by the radiation inspection apparatus 1 of the first embodiment. Further, the present embodiment can obtain the following effects (22) and (23).
(22) According to this embodiment, since the radiation detector 5D has a laminated structure of a plurality of detection elements, the thickness of each detection element between the anode electrode and the cathode electrode is reduced, and recombination of electrons and holes is performed. , The decrease in the detection signal due to the above is suppressed. Therefore, the energy resolution is improved. Further, since the time until the detection signal is output is shortened, the time resolution is also improved. Since the energy threshold can be set higher by improving the energy resolution, it is possible to remove more γ-rays whose energy has been reduced by scattering. In addition, since the time window can be reduced by improving the time resolution, the number of γ-rays that are accidentally detected within the time window can be reduced. That is, it is possible to suppress the detection of the scattering event and the random event which are the noise components to a low level, so that the image quality of the PET image can be improved.
(23) According to the present embodiment, since the radiation detector 5D has a laminated structure of a plurality of detection elements, the thickness of the detection element between the anode electrode and the cathode electrode is reduced, and the applied bias voltage is reduced. be able to. The withstand voltage of components around various wirings can be reduced by lowering the bias voltage. Further, the power supply itself can be downsized.
Third Embodiment A radiation inspection apparatus according to a third embodiment which is another embodiment of the present invention will be described below. The radiation inspection apparatus of the present embodiment differs from the radiation inspection apparatus 1 of the first embodiment only in the configuration of the detector unit. A detector unit 4B used in the present embodiment, which has a different configuration from the detector unit 4 used in the first embodiment, will be described with reference to FIGS.
The detector unit 4A has a plurality of (for example, nine) radiation detectors 5E arranged on one surface of the support substrate 6 in three rows and three columns. Each radiation detector 5E is the same semiconductor radiation detector as the radiation detector 5, and is arranged in three layers in the radial direction of the detector support member 8. In the radial direction of the detector support member 8, the radiation detectors 5Aa, 5Ab, 5Ac are on the first layer, the radiation detectors 5Ba, 5Bb, 5Bc are on the second layer, and the radiation detectors 5Ca, 5Cb, 5Cc are on the third layer. Be placed. The radiation detectors 5Aa, 5Ab, and 5Ac arranged in the circumferential direction of the detector support member 8 are stacked in the circumferential direction. Similarly, the second-layer radiation detectors 5Ba, 5Bb, 5Bc and the third-layer radiation detectors 5Ca, 5Cb, 5Cc are also stacked in the circumferential direction of the detector support member 8. This laminated structure will be described using the radiation detectors 5Aa, 5Ab, and 5Ac as an example.
The radiation detector 5Aa has four detection elements, that is, detection elements 83A, 83B, 83C, and 83D. The detection elements 83A, 83B, 83C, 83D are arranged in that order in the circumferential direction of the detector support member 8. The radiation detector 5Ab has detection elements 84A, 84B, 84C, 84D. The detection elements 84A, 84B, 84C, 84D are arranged in that order in the circumferential direction of the detector support member 8. The radiation detector 5Ac has detection elements 85A, 85B, 85C, and 85D. The detection elements 85A, 85B, 85C, 85D are arranged in that order in the circumferential direction of the detector support member 8.
A cathode electrode 86A is provided on one side surface of the detection element 83A. The detection element 83A and the detection element 83B are adjacent to each other with an anode 87A provided on the other side of the detection element 83A and one side of the detection element 83B. Here, one side surface refers to one side surface of the detection element in the circumferential direction of the detector support member 8, and the other side surface refers to the remaining side surface of the detection element in the circumferential direction of the detector support member 8. The detection element 83B and the detection element 83C are adjacent to each other with the other side of the detection element 83B and the cathode electrode 86B provided on one side of the detection element 83C interposed therebetween. The detection element 83C and the detection element 83D are adjacent to each other with an anode 87B provided on the other side of the detection element 83C and one side of the detection element 83D.
The detection element 83D and the detection element 84A are adjacent to each other with a cathode electrode 88A provided on the other side of the detection element 83D and one side of the detection element 84A. The detection element 84A and the detection element 84B are adjacent to each other with an anode 89A provided on the other side of the detection element 84A and one side of the detection element 84B. The detection element 84B and the detection element 84C are adjacent to each other with a cathode electrode 88B provided on the other side of the detection element 84B and one side of the detection element 84C. The detection element 84C and the detection element 84D are adjacent to each other with an anode electrode 89B provided on the other side of the detection element 84C and one side of the detection element 84D.
The detection element 84D and the detection element 85A are adjacent to each other with a cathode 90A provided on the other side of the detection element 84D and one side of the detection element 85A. The detection element 85A and the detection element 85B are adjacent to each other with an anode 91A provided on the other side of the detection element 85A and one side of the detection element 85B. The detection element 85B and the detection element 85C are adjacent to each other with a cathode electrode 90B provided on the other side of the detection element 85B and one side of the detection element 85C. The detection element 85C and the detection element 85D are adjacent to each other with an anode 91B provided on the other side of the detection element 85C and one side of the detection element 85D. A cathode electrode 90C is provided on the other side surface of the detection element 85D.
An earth wire 92 is connected to the cathode electrodes 86A, 86B, 88A, 88B, 90A, 90B, 90C. Wiring 93 is connected to anode electrodes 87A and 87B. Wiring 94 is connected to anode electrodes 89A and 89B. Wiring 95 is connected to anode electrodes 91A and 91B. The ground wire 92 is connected to the connector terminal 7D of the connector section 7. The wiring 93 is connected to the connector terminal 7A of the connector section 7. The wiring 94 is connected to the connector terminal 7B of the connector unit 7. The wiring 95 is connected to the connector terminal 7C of the connector section 7. Each of the radiation detectors 5E of the second and third layers is also connected to another connector terminal provided on the connector unit 7 in the same manner. The ground wire 92 and the wirings 93, 93, 93 are all installed in the support substrate 6. The large number of detector units 4B are mounted and held on the detector support portion 23 by fitting the connector terminals such as the connector terminals 7A provided on the respective connector portions 11 provided on the detector support portion 23. You. Similarly to the detector unit 4, the detector units 4B surround the hole 41 and are arranged in a large number in the circumferential direction and the axial direction of the hole 41.
By fitting the connector portion 7 into the connector portion 11, the first-layer radiation detectors 5Aa, 5Ab, and 5Ac are separately connected to three signal discriminating devices 27 in the signal discriminating unit 25. The radiation detectors 5Ba, 5Bb, 5Bc of the second layer and the radiation detectors 5Ca, 5Cb, 5Cc of the third layer are provided in the signal discrimination unit 25, and are provided for discriminating six γ-rays other than the signal discrimination device 27. Connected separately to device 32.
The radiation inspection apparatus of the present embodiment incorporating the detector unit 4B has effects (1) to (21) produced by the radiation inspection apparatus 1 of the first embodiment, effects (22) produced by the radiation inspection apparatus of the second embodiment, (23) can be obtained. Further, in the present embodiment, the following effect (24) can be obtained.
(24) According to the present embodiment, since each radiation detector 5E has a laminated structure of an even number of detector elements, both side surfaces of the adjacent radiation detectors 5E can be used as cathode electrodes. The cathode electrode can be shared by the radiation detector 5E. Therefore, the three radiation detectors 5E arranged in the circumferential direction of the detector support member 8 can be brought into close contact with each other. That is, it is possible to completely eliminate the interval between the radiation detectors 5E in the circumferential direction, and the leakage of γ-rays between the radiation detectors 5E in the circumferential direction is significantly reduced. This leads to a substantial increase in the detection efficiency of γ-rays, and shortens the inspection time.
In the first to third embodiments, a detector unit in which radiation detectors are stacked in the radial direction of the detector support member 8 (the hole 41 into which the bed 20 is inserted) is used. It has a configuration applied to a radiation inspection apparatus that can detect γ-rays and X-rays that can be applied to the radiation. However, the detector unit can also be applied to a PET radiation inspection apparatus that detects only γ-rays emitted from a subject due to a radiopharmaceutical that has penetrated into the subject without irradiating X-rays. . Also, the detector unit is
The present invention can also be applied to a radiation inspection apparatus for SPECT.
ADVANTAGE OF THE INVENTION According to this invention, the precision of the produced image can be improved and the failed radiation detector can be easily replaced.
FIG. 1 is a longitudinal sectional view of a radiation inspection apparatus according to a first embodiment which is a preferred embodiment of the present invention.
FIG. 2 is a sectional view taken along line II-II of FIG.
FIG. 3 is an enlarged view of a part III in FIG. 1;
FIG. 5 is a perspective view of the detector unit of FIG. 1;
FIG. 6 is a sectional view of the detector unit of FIG. 5 in a radial direction of a detector support member.
FIG. 7 is a detailed structural diagram of the signal discriminating apparatus of FIG. 1;
FIG. 8 is an explanatory diagram showing a processing procedure of tomographic image creation executed by the computer of FIG. 1;
9 is an explanatory diagram showing a state of γ-ray detection in the embodiment of FIG.
FIG. 10 is a perspective view of a detector unit applied to a radiation inspection apparatus of Embodiment 2 which is another embodiment of the present invention.
11 is a sectional view of the detector unit of FIG. 10 in a radial direction of the detector support member.
FIG. 12 is a perspective view of a detector unit applied to a radiation inspection apparatus according to a third embodiment which is another embodiment of the present invention.
13 is a sectional view of the detector unit of FIG. 11 in a radial direction of a detector support member.
DESCRIPTION OF SYMBOLS 1 ... Radiation inspection apparatus, 2 ... Imaging apparatus, 4, 4A, 4B ... Detector unit, 5, 5D, 5E ... Radiation detector, 7, 11 ... Connector part, 8 ... Detector support member, 13 ... X-ray source Circumferential movement device, 14 X-ray source device, 15 X-ray source drive device, 17 X-ray source, 18 subject holding device, 20 bed, 23 detector detector, 25 signal discrimination unit 27, a signal discriminator, 28, a changeover switch, 32, a γ-ray discriminator, 33, an X-ray signal processor, 34, a coincidence counter, 35, a tomographic image generator, 36, a computer, 40, a signal processor.
A detector support member extending in a longitudinal direction of the bed supporting the subject and arranged around the bed; and a plurality of radiation detection units arranged in the longitudinal direction of the bed and around the bed, wherein the detection is performed. A radiation detection apparatus including the plurality of detector units detachably attached to a vessel support member,
The radiation inspection apparatus, wherein the detector unit has a plurality of radiation detectors for detecting radiation, and the radiation inspection apparatus further includes another radiation detector for detecting the radiation passing through a certain radiation detector. .
An annular detector support member extending in the longitudinal direction of the bed supporting the subject and disposed around the bed; and a plurality of radiation detectors disposed in the longitudinal direction of the bed and in the circumferential direction of the detector support member. A radiation detection device including the plurality of detector units detachably attached to the detector support member, the unit comprising:
The radiation inspection apparatus, wherein the detector unit has a plurality of radiation detectors for detecting radiation, and a plurality of the radiation detectors are arranged at different positions in a radial direction of the detector support member.
The detector unit, a detector support substrate detachably attached to the detector support member, a plurality of the certain radiation detectors and a plurality of the other radiation detectors installed on the detector support substrate, The radiation inspection apparatus according to claim 1, further comprising: a plurality of wirings provided on the detector support substrate, connected to the radiation detectors, and transmitting a detection signal output from the radiation detector.
The radiation inspection apparatus according to any one of claims 1 to 3, further comprising an image creation device that creates an image of the subject using an output signal of the radiation detector.
A detector support member extending in a longitudinal direction of the bed supporting the subject and arranged around the bed; and a plurality of radiation detection units arranged in the longitudinal direction of the bed and around the bed, wherein the detection is performed. A radiation detection device including the plurality of detector units detachably attached to a vessel support member,
The detector unit has a plurality of radiation detectors for detecting γ-rays, provided with another radiation detector for detecting the γ-rays passed through a certain radiation detector,
A radiation inspection apparatus comprising a signal processing device for a γ-ray detection signal output from the radiation detector.
The detector unit, a detector support substrate detachably attached to the detector support member, a plurality of the certain radiation detectors and a plurality of the other radiation detectors installed on the detector support substrate, A plurality of wirings provided on the detector support substrate and connected to the radiation detectors and transmitting a γ-ray detection signal output from the radiation detector,
The radiation inspection apparatus according to claim 5, wherein the signal processing apparatus inputs the γ-ray detection signal transmitted through the wiring.
The radiation inspection apparatus according to claim 5, further comprising: an image creating apparatus that creates an image including a site where the radiopharmaceuticals in the subject are accumulated, using output information from the signal processing apparatus.
The radiation inspection apparatus according to claim 6, wherein the wiring is provided in the detector support substrate.
A detector support member that extends in the longitudinal direction of the bed supporting the subject and is arranged around the bed, an X-ray source that moves around the bed and emits X-rays, A radiation detection device including a plurality of radiation detection units arranged around the bed and including the plurality of detector units detachably attached to the detector support member,
The detector unit has a plurality of radiation detectors for detecting radiation, and is provided with another radiation detector for detecting the radiation passing through a certain radiation detector,
A radiation inspection apparatus, wherein at least the certain radiation detector outputs both the X-ray detection signal and the γ-ray detection signal.
The radiation inspection apparatus according to claim 9, further comprising an X-ray source moving device that moves the X-ray source in the longitudinal direction.
The radiation inspection apparatus according to claim 9 or 10, wherein the certain radiation detector and the other radiation detector are arranged in a straight line.
12. A tomographic image creating device for creating a tomographic image using first information obtained from the γ-ray detection signal and second information obtained from the X-ray detection signal. A radiation inspection apparatus according to claim 1.
A first γ-ray signal processing device that inputs the γ-ray detection signal from the first radiation detector that outputs both the X-ray detection signal and the γ-ray detection signal, and an X that inputs the X-ray detection signal A line signal processing device is provided for each of the first radiation detectors,
A second γ-ray signal processing device that inputs the γ-ray detection signal from the second radiation detector that outputs the γ-ray detection signal without outputting the X-ray detection signal is provided for each of the second radiation detectors ,
The respective output signals of each of the first γ-ray signal processing devices and each of the second γ-ray signal processing devices are input, and the respective positional information of the pair of radiation detectors that have detected the γ-rays within a set time, and Having a counting device to output each information of the counting information of the γ-rays,
The radiation according to any one of claims 9 to 11, further comprising a tomographic image creating device that creates tomographic image information using the position information, the counting information, and output information of each of the X-ray signal processing devices. Inspection equipment.
The radiation inspection apparatus according to any one of claims 1 to 13, wherein the radiation detector is a semiconductor radiation detector.
15. The radiation inspection apparatus according to claim 14, wherein the semiconductor radiation detector includes three or more semiconductor elements having at least two surfaces, and an anode electrode and a cathode electrode are alternately arranged between different semiconductor elements.
The semiconductor radiation detector has a stacked structure of an even number of semiconductor elements, forms a common anode electrode and a cathode electrode between adjacent semiconductor elements in the semiconductor radiation detector, and opposes both surfaces of the adjacent semiconductor radiation detector. 15. The radiation inspection apparatus according to claim 14, wherein a common cathode electrode is formed on the radiation inspection apparatus.
JP2002307785A 2002-10-23 2002-10-23 Radiation inspection equipment Expired - Fee Related JP4093013B2 (en)
JP2002307785A JP4093013B2 (en) 2002-10-23 2002-10-23 Radiation inspection equipment
US10/688,977 US7154989B2 (en) 2002-10-23 2003-10-21 Radiological imaging apparatus
EP20030023925 EP1413898A1 (en) 2002-10-23 2003-10-21 Radiological imaging apparatus
US11/370,915 US7218701B2 (en) 2002-10-23 2006-03-09 Radiological imaging apparatus
US11/516,729 US20070058773A1 (en) 2002-10-23 2006-09-07 Radiological imaging apparatus
JP2004144529A true JP2004144529A (en) 2004-05-20
JP4093013B2 JP4093013B2 (en) 2008-05-28
ID=32064327
JP2002307785A Expired - Fee Related JP4093013B2 (en) 2002-10-23 2002-10-23 Radiation inspection equipment
US (3) US7154989B2 (en)
EP (1) EP1413898A1 (en)
JP (1) JP4093013B2 (en)
JP2007178364A (en) * 2005-12-28 2007-07-12 Hitachi Ltd Nuclear medicine diagnostic equipment
WO2010046983A1 (en) * 2008-10-23 2010-04-29 株式会社島津製作所 Particle beam treatment apparatus
US7750303B2 (en) 2005-02-22 2010-07-06 Hitachi, Ltd. Radiological imaging apparatus and positron emission tomographic apparatus
JP2012524591A (en) * 2009-04-22 2012-10-18 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 Imaging measurement system with printed organic photodiode array
JP5187401B2 (en) * 2008-12-16 2013-04-24 株式会社島津製作所 Particle beam therapy system
FR2872295B1 (en) 2004-06-28 2007-02-09 Commissariat Energie Atomique Tomography with specific shape detectors
JP3858044B1 (en) * 2005-09-09 2006-12-13 株式会社アクロラド Radiation detection module, printed circuit board, and positron emission tomography apparatus
US7623625B2 (en) * 2007-04-11 2009-11-24 Searete Llc Compton scattered X-ray visualization, imaging, or information provider with scattering event locating
US8487264B2 (en) * 2008-07-31 2013-07-16 Shimadzu Corporation Radiation tomography apparatus
CN102246057A (en) 2008-12-10 2011-11-16 皇家飞利浦电子股份有限公司 Autonomous detector module as a building block for scalable pet and spect systems
PL2753920T3 (en) 2011-09-07 2018-09-28 Rapiscan Systems, Inc. X-ray inspection system that integrates manifest data with imaging/detection processing
WO2017025842A1 (en) * 2015-08-07 2017-02-16 Koninklijke Philips N.V. Hybrid pet / ct imaging detector
CN105380672A (en) * 2015-10-28 2016-03-09 沈阳东软医疗系统有限公司 PET detection system and method for increasing resolution ratio of PET detection system
EP3374803A4 (en) * 2015-11-12 2019-07-31 Prismatic Sensors Ab High-resolution computed tomography using edge-on detectors with temporally offset depth-segments
GB2564038A (en) 2016-02-22 2019-01-02 Rapiscan Systems Inc Systems and methods for detecting threats and contraband in cargo
US10448909B2 (en) 2016-03-08 2019-10-22 Koninklijke Philips N.V. Combined X-ray and nuclear imaging
CA1117228A (en) 1979-08-27 1982-01-26 Montreal Neurological Institute Positron annihilation imaging device using multiple offset rings of detectors
JPS6252479A (en) 1985-08-31 1987-03-07 Shimadzu Corp Ring spect apparatus
CA1245375A (en) * 1986-06-06 1988-11-22 Roger Lecomte Scintillation detector for tomographs
JP3404080B2 (en) 1993-06-30 2003-05-06 株式会社島津製作所 Positron CT system
JP3427584B2 (en) * 1995-03-22 2003-07-22 三菱電機株式会社 Wide-area radiation detector
JP4049829B2 (en) 1995-06-23 2008-02-20 株式会社東芝 Radiation diagnostic equipment
CA2252993C (en) * 1998-11-06 2011-04-19 Universite De Sherbrooke Detector assembly for multi-modality scanners
US20030107147A1 (en) * 2000-06-16 2003-06-12 Avery Dennison Corporation Process and apparatus for making fuel cell plates
US7297958B2 (en) * 2001-12-03 2007-11-20 Hitachi, Ltd. Radiological imaging apparatus
US6661866B1 (en) * 2002-08-28 2003-12-09 Ge Medical Systems Global Technology Company, Llc Integrated CT-PET system
2002-10-23 JP JP2002307785A patent/JP4093013B2/en not_active Expired - Fee Related
2003-10-21 US US10/688,977 patent/US7154989B2/en not_active Expired - Fee Related
2003-10-21 EP EP20030023925 patent/EP1413898A1/en not_active Withdrawn
2006-03-09 US US11/370,915 patent/US7218701B2/en not_active Expired - Fee Related
2006-09-07 US US11/516,729 patent/US20070058773A1/en not_active Abandoned
JP5120459B2 (en) * 2008-10-23 2013-01-16 株式会社島津製作所 Particle beam therapy system
CN102164635B (en) * 2008-10-23 2014-01-15 株式会社岛津制作所 Particle beam treatment apparatus
JP4093013B2 (en) 2008-05-28
US20070058773A1 (en) 2007-03-15
US7218701B2 (en) 2007-05-15
US20040125915A1 (en) 2004-07-01
US7154989B2 (en) 2006-12-26
US20060153339A1 (en) 2006-07-13
EP1413898A1 (en) 2004-04-28
US8073525B2 (en) 2011-12-06 Combined PET/MRT unit and method for simultaneously recording PET images and MR images
US20010040219A1 (en) 2001-11-15 Apparatus and method for breast cancer imaging
EP1952180B1 (en) 2017-01-04 Dynamic spect camera
US6597940B2 (en) 2003-07-22 Methods of detecting occlusion of the coronary artery system and imaging the heart
US7251523B2 (en) 2007-07-31 Tomogram creating device and radiation examining apparatus
JP2004512512A (en) 2004-04-22 System and method for nuclear imaging using feature enhanced transmission imaging
US7521681B2 (en) 2009-04-21 Non-rotating transaxial radionuclide imaging
2006-04-21 RD01 Notification of change of attorney
2008-02-06 TRDD Decision of grant or rejection written
2008-03-17 FPAY Renewal fee payment (prs date is renewal date of database)
2014-03-14 LAPS Cancellation because of no payment of annual fees