Source: http://www.google.com/patents/US7964849?dq=6,460,050
Timestamp: 2016-05-02 00:13:37
Document Index: 274686649

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Patent US7964849 - Nuclear medical diagnosis apparatus - Google PatentsSearch Images Maps Play YouTube News Gmail Drive More »Sign inPatentsA PET apparatus comprises a plurality of detector units in the circumferential direction, wherein the detector unit includes a plurality of unit substrates therein, and wherein the unit substrate includes: a plurality of detectors upon which a γ-ray is incident; and an analog ASIC and digital ASIC for...http://www.google.com/patents/US7964849?utm_source=gb-gplus-sharePatent US7964849 - Nuclear medical diagnosis apparatusAdvanced Patent SearchPublication numberUS7964849 B2Publication typeGrantApplication numberUS 12/837,877Publication dateJun 21, 2011Priority dateSep 29, 2006Fee statusPaidAlso published asUS7795590, US8148695, US20090114826, US20100282974, US20110215254Publication number12837877, 837877, US 7964849 B2, US 7964849B2, US-B2-7964849, US7964849 B2, US7964849B2InventorsIsao Takahashi, Takafumi Ishitsu, Yuichiro Ueno, Tomoyuki SeinoOriginal AssigneeHitachi, Ltd.Export CitationBiBTeX, EndNote, RefManPatent Citations (19), Non-Patent Citations (1), Referenced by (1), Classifications (12), Legal Events (1) External Links: USPTO, USPTO Assignment, EspacenetNuclear medical diagnosis apparatus
US 7964849 B2Abstract
a control unit which, based on the number of times the output signal from the detector is determined as a noise, determines a relevant radiation detector as faulty, and which controls so as not to process an output signal from the radiation detector that is determined as faulty, and when it is determined that the radiation detector that had been determined as faulty has returned to a normal state, the control unit processes a detection signal from the radiation detector that has returned to the normal state.
2. The nuclear medical diagnostic apparatus according to claim 1, wherein
when it is determined that the radiation detector that had been determined as faulty has returned to the normal state, the control unit resets the information on an abnormal detector and processes the detection signal from the radiation detector that has returned to the normal state.
3. A nuclear medical diagnosis apparatus, comprising an image pickup device including: a plurality of radiation detectors that detect radiation from a test object or radiation passing through the test object; and a signal processing device connected to each of the radiation detectors, the signal processing device processing an output signal from the radiation detector, the nuclear medical diagnosis apparatus generating an image based on information on detected radiation outputted from the signal processing device of the image pickup device, wherein
a control unit which, based on determination as a noise, determines a relevant radiation detector as faulty, and which controls so as not to process an output signal from the radiation detector that is determined as faulty, and when it is determined that the radiation detector that had been determined as faulty has returned to a normal state, the control unit processes a detection signal from the radiation detector that has returned to the normal state.
4. The nuclear medical diagnosis apparatus according to claim 3, wherein
when it is determined that the radiation detector that had been determined as faulty has returned to the normal state, the control unit resets information on an abnormal detector and processes the detection signal from the radiation detector that has returned to the normal state.
5. The nuclear medical diagnosis apparatus according to claim 3, wherein
the determination unit determines whether an output signal from the radiation detector is a noise, based on an energy.
6. A control method of a nuclear medical diagnosis apparatus which generates an image based on information on detected radiation outputted from a signal processing device of an image pickup device, wherein
the signal processing device executes the steps of:
determining whether an output signal from a radiation detector is an intended radiation detection signal or a noise;
determining, a relevant radiation detector as faulty based on the determination as a noise;
controlling so as not to process an output signal from the radiation detector that is determined as faulty;
when it is determined that the radiation detector that had been determined as faulty has returned to a normal state, processing a detection signal from the radiation detector that has returned to the normal state.
when it is determined that the radiation detector that had been determined as faulty has returned to the normal state, the signal processing device resets information on an abnormal detector and processes the detection signal from the radiation detector that has returned to the normal state.
the signal processing device determines whether an output signal from the radiation detector is a noise, based on an energy.
This is a continuation application of U.S. patent application Ser. No. 11/861,977, filed Sep. 26, 2007, now allowed, the contents of which is hereby incorporated by reference into this application.
For this reason, the conventional technique described in JP-A-2006-98411 (paragraphs [0032], and [0035] to [0039]) uses the method for detecting an abnormal semiconductor radiation detector and excluding an output signal therefrom, wherein in a PET apparatus or SPECT apparatus equipped with a plurality of semiconductor radiation detectors, semiconductor radiation detectors are arranged so as to surround the circumference of the body axis of a test object and also to be in multiple layers in the radial direction. Here, with respect to γ-rays in the radial direction passing through the semiconductor radiation detectors in multiple layers, a ratio between signals outputted by the semiconductor radiation detectors in each layer is used to determine which semiconductor radiation detector on which layer is abnormal when the ratio deviates from a predetermined ratio by a specified amount or more.
As shown in FIG. 2, the data processing device 12 includes a non-illustrated storage device, a simultaneous measurement device 12A, and a tomogram information preparation device 12B. The data processing device 12 captures a packet data (information on detected radiation). The simultaneous measurement device 12A carries out simultaneous measurement based on the packet data, in particular, a data of the detection time, and the detector ID. Then, the simultaneous measurement device 12A identifies a detection position of a γ-ray of 511 keV and stores the same into the storage device. The tomogram information preparation device 12B prepares functional images based on the identified position, and displays the same on the display device 13 a. Incidentally, the test object P is given fluoro-deoxy-glucose (FDG) containing radiopharmaceutical, e.g., 18F with a half-life period of 110 minutes. From the body of the test object P, a pair of 511 keV γ-rays (annihilation γ-rays) are emitted in approximately 180� direction with respect to each other at the time of annihilation of a positron emitted from FDG.
As shown in the (a) of FIG. 6, in the detector substrate 20A, on one side of a substrate body 20 a, for example, 16 detectors 21 are disposed in a horizontal row in the (a) of FIG. 6 corresponding to the body axis direction of the test object P, and furthermore, four rows of detectors 21 are disposed in the vertical direction in the (a) of FIG. 6 corresponding to the radial direction with respect to the body axis of the test object P, namely, a total of 64 detectors 21 (16 horizontally�4 vertically) are disposed in a grid pattern. Moreover, as shown in the (b) of FIG. 6, the detectors 21 are disposed similarly on the other surface of the detector substrate 20A, as well, and thus a total of 128 detectors 21 on both surfaces are disposed in one detector substrate 20A.
Moreover, in the detector 21, the surfaces of the electrodes A and C shown in the (b) of FIG. 5 may be arranged in parallel to the surface of the substrate body 20 a, or the surfaces of the electrodes A and C may be arranged perpendicular to the surface of the substrate body 20 a. For the purpose of collecting charges, a potential difference (voltage) of 500 V is applied between the anode A and cathode C of each detector 21 by means of a high voltage power supply 27 (see FIG. 8), for example. This voltage is supplied from the ASIC substrate 20B side to the detector substrate 20A side via the connector C1 (see the (a) of FIG. 6). Moreover, a γ-ray detection signal outputted when each detector 21 detects a γ-ray is supplied to the ASIC substrate 20B side via the connector C1. For this reason, in the substrate body 20 a of the detector substrate 20A, there are provided non-illustrated on-board wiring (used for voltages applied to the detector, used for signal transfer) that connects the connector C1 to each detector 21. This on-board wiring has a multilayer structure. The detector substrate 20A includes the connector C1 connected to the on-board wiring to be connected to each detector 21, and is connected to a connector C1 of the later-described ASIC substrate 20B.
The peak hold circuits 24 e, 24 g of the analog signal processing circuit 33 that received the peak hold control signal will carry out peak hold processing to the signals inputted from the waveform shaper circuits 24 d, 24 f. Then, upon receipt of a reset signal from the address calculation part 36 a after a predetermined time elapsed, the peak hold circuits 24 e, 24 g cancels the peak hold processing. ADCs 25A, 25B convert the pulseheight values (voltage values) VE1, VE2 outputted from the peak hold circuits 24 e, 24 g of the analog signal processing circuit 33 corresponding to the detector ID inputted from the address calculation part 36 a, into a digital signal and output the same to the noise determination part 36 e. The noise determination part 36 e includes a non-illustrated nonvolatile memory and stores therein a correlation data between two pulseheight values VE1, VE2 used for determining whether a relevant detection signal is a noise or not. Thus, the noise determination part 36 e determines whether the relevant signal is a noise signal or a γ-ray detection signal based on the inputted pulseheight values VE1, VE2 (the details will be described later). If determined as a γ-ray detection signal, the noise determination part 36 e will not output a noise count signal but output the pulseheight values VE1, VE2 to the detection energy correcting part 36 c. The detection energy correcting part 36 c includes a non-illustrated nonvolatile memory and stores therein each correction value of the gain and offset of each detector 21 and analog ASIC 24 based on the calibration data collected in advance. Then, using the above-described correction value corresponding to the detector ID inputted from the address calculation part 36 a, the detection energy correcting part 36 c calculates pulseheight value VE1′ and VE2′ that are corrected from the pulseheight values VE1, VE2 and outputs the same to the detection time correcting part 36 b. Moreover, the detection energy correcting part 36 c generates, based on the corrected pulseheight value VE1′ and VE2′, the information on the detection energy value corresponding to an energy of the detected γ-ray, and outputs the same to the packet data generation part 36 d. If determined as a noise signal, the noise determination part 36 e outputs a noise count signal to the noise counting part 36 f along with the detector ID, and outputs a reset signal to the packet data generation part 36 d but does not output the pulseheight values VE1, VE2 to the detection energy correcting part 36 c. The noise counting part 36 f includes a non-illustrated nonvolatile memory or volatile memory and counts and stores therein the noise count for each detector ID. If the noise count is equal to or greater than a specified reference value, the noise counting part 36 f determines a relevant detector 21 as abnormal and outputs this abnormality determination to the control part 36 g. Moreover, the control part 36 g includes a non-illustrated nonvolatile memory and stores therein the abnormality determination output from the noise counting part 36 g. Based on this, the control part 36 g controls data processing in the detector control part 36 with respect to an output signal from the detector 21 corresponding to the detector ID that is determined as abnormal.
The detection time correcting part 36 b corrects the detection time information inputted from the address calculation part 36 a based on the pulseheight values VE1′, VE2′ inputted and corrected from the detection energy correcting part 36 c, and outputs the same to the packet data generation part 36 d. The packet data generation part 36 d appends the corrected detection time information and the detector ID to the information on the detection energy value from the detection energy correcting part 36 c, and thereby generates a packet data (information on the detected γ-ray, information on the detected radiation), which is digital information, and outputs the same to the data transfer part 37. The data transfer part 37, for example, periodically transmits the packet data outputted from the packet data generation part 36 d of each detection signal processing part 34 to the unit integration FPGA 31 (Field Programmable Gate Array, hereinafter, referred to as FPGA) provided outside the enclosure 30 of the detector unit 2 (see FIG. 15, FIG. 16) that houses twelve coupling substrates 20 therein. FPGA 31 transmits these digital information to the data processing device 12 via information transmission wiring connected to a connector 38.
In addition, the upper and the lower of the enclosure 30 are referred to the positional relation when the enclosure 30 is removed from the camera 11, and as shown in FIG. 2, when the enclosure 30 is provided in the camera 11, the upper and the lower will be reversed, or the upper and the lower will be rotated by 90� to be at a horizontal position or at a diagonal position.
Next, the high voltage power supply device PS for supplying a charge collecting voltage is described. As shown in FIG. 10, in the detector unit 2, the high voltage power supply device PS for supplying a charge collecting voltage to each detector 21 is mounted in a space formed by a partition 30 c composed of a conductor metal material inside the enclosure 30 on the rear surface side of FPGA 31. This high voltage power supply device PS is supplied with a low voltage power, and is adapted to boost up this voltage to 500 V using a non-illustrated voltage boosting type DC-DC converter, and to supply the same to each detector 21. Incidentally, 64 detectors 21 are provided on one side and 128 detectors 21 are provided on both sides per one detector substrate 20A. Then, twelve coupling substrates 20 are housed in one enclosure 30. Accordingly, the high voltage power supply device PS supplies a voltage to 128�12=1536 detectors 21.
When a γ-ray enters the detector 21, the detector 21 generates an electron-hole pair corresponding to an absorbed energy, and the electron and hole are induced by an electric field generated by an applied voltage, and thereby the electron will transfer to the anode A side and the hole will transfer to the cathode C side. This transfer of the electron and the hole results in the current pulse IA occurring at the input side of the preamplifier 24 a. The example here shows the case where the energy of the incident radiation is 511 keV, wherein all the energy is absorbed (on the left in the view) and the half the energy is absorbed and the remaining half energy is scattered (on the right in the view), at the same position between the anode A and the cathode C. About the current pulse IA of FIG. 13C, in either case, it takes the same time to for the generated electron and hole to transfer to the anode A and the cathode C, respectively, however, in the latter case the detector 21 outputs the current half the former case.
For example, the waveform of the voltage signal VB at the contribution of electron of 100% is described. When the detected energy changes, for example, when one energy is 511 keV and the other energy is 255 keV, the number of electrons occurring in the vicinity of the cathode C inside the detector 21 changes, and the both cases show no difference in the time interval (transfer time of the electron) to of the current pulse IA but shows a difference in the current value (pulse height), so that in the waveform of the voltage signal VB at the input side of the comparator 24 b, the energy of 255 keV shows a smaller gradient than the energy of 511 keV. Accordingly, when compared with a specified voltage threshold VLD in the comparator 24 b, the energy of 255 keV delays by a time t2 as compared with the energy of 511 keV.
Then, the region 80 is a region of noise signals. The noise signal does not necessarily have a 8 function-like spike waveform, but may have a broad waveform in time scale.
When the noise determination part 36 e, based on the inputted pulseheight values (voltage values) VE1, VE2, determines that the γ-ray detection signal VS1 is a γ-ray detection signal resulting from the intended γ-ray detection, i.e., that the γ-ray detection signal VS1 is not a noise signal, the noise determination part 36 e will not output a noise count signal but output two pulseheight values VE1, VE2 to the detection time correcting part 36 b and output the pulseheight value VE1 to the packet data generation part 36 d. When the noise determination part 36 e determines that the γ-ray detection signal VS1 is a noise signal, the noise determination part 36 e will output a noise count signal to the noise counting part 36 f and output a reset signal to the packet data generation part 36 d, but will not output the pulseheight values VE1, VE2 to the detection time correcting part 36 b and will not output the pulseheight value VE1 to the packet data generation part 36 d. Accordingly, if determined as a noise signal, the detection time correcting part 36 b will not carry out the later-described correction of detection time information and the packet data generation part 36 d will not output an unnecessary data to the data processing device 12 that carries out simultaneous measurement processing, so that the load of the digital ASIC 26 is reduced and the load of signal processing on the downstream side is also reduced.
The control part 36 g includes a nonvolatile memory function. Upon receipt of the abnormality determination, the control part 36 g stores an abnormality determination time based on a system clock and the detector ID, and inputs and stores this detector ID to the address calculation part 36 a. Even if the timing signal VT of a channel of the detector 21 corresponding to the stored detector ID is inputted, the address calculation part 36 a will not carry out address calculation processing and will not output the detector ID, thereby preventing the data processing in the detector control part 36. Namely, since the address calculation part 36 a will not output an ADC control signal to the abnormal detector 21, the pulseheight value will not be read by ADCs 25A, 25B and the calculation processing using VE1, VE2 will not be carried out.
In addition, in place of receiving abnormality determination from the noise counting part 36 f, the control part 36 g may check the noise counting part 36 f at a predetermined cycle, and check whether the noise count exceeds a specified reference value, which is set in advance, to make abnormality determination and control the reset of the count of the noise counting part 36 f. Moreover, the method for stopping the signal processing to the detector 21 is not limited to the above-described method. For example, the high voltage power supply 27 individually supplied to the detector 21 may be turned off, or the address calculation part 36 a may append an abnormality flag, i.e., identification information indicating to the packet data generation part 36 d that the relevant detection signal is faulty, for a packet data of the relevant detector ID, instead of stopping the address calculation. In this case, the data processing part 12 in the subsequent stage detects the abnormality flag contained in the packet data and excludes the relevant packet data so as not to be subjected to the signal processing.
A SPECT apparatus 51 comprises a pair of radiation camera parts 52, a rotating support stand 57, a data processing device 58, and an operator console 13A. The radiation camera parts 52 are disposed facing to each other on the rotating support stand 57 at positions shifted by 180� in the circumferential direction. Specifically, each unit supporting member 56 of the respective radiation camera parts 52 is mounted to the rotating support stand 57 at a position separated by 180� in the circumferential direction. A plurality of detector units 102 each including twelve coupling substrates are removably mounted to the respective unit supporting members 56.
The detector control part 136 includes the address calculation part 36 a, the detection energy correcting part 36 c, a packet data generation part 136 d, the noise determination part 36 e, the noise counting part 36 f, and the control part 36 g. Upon receipt of the detection time information corresponding to the timing signal VT′ obtained when a γ-ray is detected, from the timing detection part 135, the address calculation part 36 a identifies a relevant detector ID, and outputs the detector ID and the detection time information to the detection energy correcting part 36 c, the packet data generation part 136 d, and the noise determination part 36 e. That is, the address calculation part 36 a stores the detector ID corresponding to each timing detection part 135 connected to the address calculation part 36 a, whereby when the detection time information is inputted from a certain timing detection part 135, the address calculation part 36 a can identify an detector ID corresponding to the timing detection part 135. This is possible because the timing detection part 135 is provided for each detector 21.
Furthermore, after the trigger signal is inputted the address calculation part 36 a, the address calculation part 36 a outputs a peak hold control signal to the analog signal processing circuit 133 including the above-described identified detector ID, and also outputs the detector ID and the ADC control signal to ADCs 25A, 25B. Upon receipt of the peak hold control signal, the peak hold circuits 24 e, 24 g of the analog signal processing circuit 133 carry out peak hold processing to the signal inputted from the waveform shaper circuits 24 d, 24 f. Then, upon receipt of a reset signal from the address calculation part 36 a after a predetermined time, the peak hold circuits 24 e, 24 g cancel the peak hold processing. The ADCs 25A, 25B convert the pulseheight values (voltage values) VE1, VE2 outputted from the peak hold circuits 24 e, 24 g of the analog signal processing circuit 133 corresponding to the detector ID inputted from the address calculation part 36 a into a digital signal and output the same to the noise determination part 36 e. These pulseheight values VE1, VE2 are inputted to the noise determination part 36 e. The noise determination part 36 e determines whether the relevant detection signal is a noise signal or a γ-ray detection signal based on the correlation between two pulseheight values VE1, VE2. If determined as a γ-ray detection signal, the noise determination part 36 e will output the pulseheight values VE1, VE2 to the detection energy correcting part 36 c but will not output a noise count signal to the noise counting part 36 f. By using a correction value corresponding to the gains and offsets of the detector 21 and analog ASIC 124 corresponding to the detector ID inputted from the address calculation part 36 a, the detection energy correcting part 36 c calculates pulseheight values VE1′, VE2′ that are corrected from the pulseheight values VE1, VE2, and generates information on the detection energy value corresponding to the energy of the detection γ-ray, and outputs the same to the packet data generation part 136 d. When determined as a noise signal, the noise determination part 36 e outputs a noise count signal to the noise counting part 36 f along with the detector ID, and outputs a reset signal to the packet data generation part 36 d. (Operation of Detector Output Signal Processing Control Part)
A rotation angle detected by an angle gauge (not shown) connected to the rotating shaft of a motor (not shown) that rotates the rotating support stand 57 is inputted to the data processing device 58. This rotation angle indicates the rotation angle of each radiation camera part 52, specifically indicating the rotation angle of each detector 21. On the basis of this rotation angle, the data processing device 58 calculates the position (positional information) on the pivoting track of each pivoting detector 21. Accordingly, a position (position coordinate) of the detector 21 obtained when a γ-ray is detected can be calculated. On the basis of the detector ID that detected a γ-ray, the data processing device 58 counts a γ-ray for which the detection energy value is equal to or greater than a set value. The detection energy value here is a summation of the detection energy value of each γ-ray detection signal if there is coincidence in a plurality of detectors 21 (four detectors 21 arranged side by side in a straight line in the (a) of FIG. 6) positioned on an extension of the radiation path of the collimator 55. This counting is carried out on each of the areas corresponding to increments of 0.50� with respect to the rotational center of the rotating support stand 57.
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