JP5238452B2 - Radiation detection apparatus and X-ray CT apparatus using the same - Google Patents

Description

  The present invention relates to a radiation detection apparatus that detects radiation such as X-rays and γ-rays, and in particular, a radiation detection apparatus in which a plurality of radiation detection elements that detect radiation as electrical signals are arranged in a matrix and X using the same Related to line CT equipment.

  Currently, in an X-ray CT system, multiple rows of radiation detection element arrays are arranged in the slice direction (that is, a two-dimensional array), and two-dimensional radiation data is collected by one radiation exposure. A multi-slice X-ray CT apparatus equipped with the obtained two-dimensional radiation detector has been put into practical use.

  The radiation detector of this multi-slice X-ray CT system includes an indirect conversion detector that combines a phosphor element such as a ceramic scintillator and a photodiode, and X-ray irradiation to generate electron-hole pairs in the semiconductor. There is a direct conversion type detector that takes out this as an electrical signal, and the radiation detector is configured by arranging a plurality of radiation detection elements in an arc shape centered on the focal point of the X-ray tube.

  In the multi-slice X-ray CT apparatus equipped with the radiation detector having such a configuration, the number of detection elements (slice number) in the slice direction is practically 32 slices and 64 slices, and further 128 slices and 256 slices are provided. The number of slices tends to increase into slices.

  Under such circumstances, for example, when an indirect conversion type detection method is adopted, a wiring board includes a scintillator array in which a plurality of matrices are formed in the slice direction and the channel direction, and a photodiode array having the same matrix as the scintillator array. In the method of stacking on the top, the area of the photodiode array increases, so that the probability that defective photodiode cells are included in one photodiode array increases. That is, usually, one silicon wafer is composed of a plurality of photodiode cells, and a plurality of photodiode arrays are manufactured by cutting the plurality of photodiode cells every predetermined number of cells.

  However, defective photodiode cells are included in the silicon wafer at a certain rate, and the probability of including defective cells increases as the area of the photodiode array increases.

  For this reason, when a photodiode array having a large area is manufactured, the yield is lowered, resulting in an increase in cost.

  Further, as the number of slices increases, the number of wirings for extracting detected signals also increases so that the number of slices is limited in terms of the number of wirings.

  That is, in the photodiode array, a plurality of light receiving cells that receive scintillation light are arranged in a matrix, and each cell of the photodiode array is partitioned by a dead zone region.

  The output signal from each cell passes through the signal line wired in the dead zone region between the channel direction cells and is taken out to the end in the slice direction of the photodiode array. However, as the number of slices increases, Since the number also increases, it becomes difficult to wire the signal line to the dead zone.

  Such a problem is also the same in the direct conversion detector, and as a method for solving the problem, a tiling method for dividing a radiation detection element into a matrix of a specific shape is disclosed in Patent Document 1. Has been.

  This is because when manufacturing an M-slice × N-channel radiation detector array module (for example, 64 columns × 24 rows array), a plurality of M × N photodiode arrays (for example, 32 columns) smaller than M × N. × 24-row array) are mounted side by side on a wiring board, a scintillator array is mounted on these photodiode arrays, and the photodiode array and the scintillator array are fixed with a transparent adhesive, and the M × N radiation This is a method of configuring a detection element array module.

  With this method, the size of one photodiode array can be reduced, so that the manufacturing yield can be improved and an increase in signal lines due to an increase in the number of slices can be suppressed.

  However, in this method, after the first scintillator array is bonded, the adhesive protrudes around the array. Then, when trying to bond the second scintillator array, the adhesive that protrudes when the first scintillator array is bonded becomes an obstacle, making it difficult to adhere the arrays to each other. It becomes impossible to mount on the substrate with high positional accuracy. That is, it is necessary to provide a gap between the photodiode arrays in consideration of the accuracy of mounters and jigs to be arranged, workability of bonding work, and the like.

Japanese Patent Laid-Open No. 2004-8406

  As described above, recent multi-slice X-ray CT apparatuses tend to have a very large number of multi-slices such as 128 slices and 256 slices of 64 slices or more. In this case, it is desirable to construct a system that is advantageous in terms of economy by sharing as many parts as possible of the radiation detection devices of the various slice X-ray CT apparatuses.

  In addition, in the X-ray CT radiation detection apparatus, taking an indirect conversion type as an example, a two-dimensionally arranged scintillator array is similarly stacked on a two-dimensionally arranged photodiode array. A radiation detector element is composed of a pair of an individual scintillator element that is bonded with a transparent adhesive and constitutes the scintillator array, and a photodiode element that constitutes the photodiode array. The radiation detector elements are arranged two-dimensionally to constitute a radiation detector element array.

  Further, one or a plurality of radiation detector element arrays are mounted on the photodiode array holding substrate and arranged to constitute a radiation detector module.

  The radiation detector module detects radiation according to the intensity of radiation incident on the radiation detector element array. Since these radiation detection signals are analog signals, the analog signals are converted into digital signals by a data acquisition system DAS (Data Acquisition System), and the digital signals are subjected to image processing to generate a CT image.

  The DAS includes an integrator, a current / voltage converter, an analog / digital converter, etc. for a plurality of radiation detector elements as one ASIC (Application Specific Integrated Circuit) chip (hereinafter referred to as a DAS chip). It consists of a DAS chip, a circuit for inputting control signals, a power supply circuit, and the like.

  In the DAS chip, for example, the DAS circuit is miniaturized so that the number of channels of the radiation detection signal is for 32 channels or 64 channels.

  A plurality of the radiation detector modules are arranged in the channel direction, and the outputs of the plurality of radiation detector modules are input to the DAS to constitute a radiation detection apparatus for an X-ray CT apparatus.

  In the radiation detection apparatus having such a configuration, for example, when extending to a slice for 64 slices, a slice for 128, and a slice for 256 using a plurality of radiation detector modules and DAS chips of a radiation detector for 32-slice type, Although the DAS chip can be shared, when the radiation detector module is provided with a gap between the photodiode arrays using the tiling method described in Patent Document 1, the multi-slice type is unique.

  In other words, the DAS chip for 32 slices is 2 for the 64-slice type, 4 for the 128-slice type, and 8 for the 256-slice type. Multiple 32-slice chips can be used.

  However, regarding the radiation detector module, if a gap is provided between the photodiode arrays using the tiling method as described above, the radiation detector module is radiated from an X-ray tube that divides the surface of the radiation detector in the slice direction at equal intervals. The spread angle (cone angle) pitch in the column direction of cone beam X-rays does not match the radiation detector element pitch in the slice direction (column direction) of the radiation detector.

  The detection error due to the mismatch can be corrected by correcting the positional information of the radiation detection element pitch between the arrays. However, if an electrode pad for electrically connecting the output terminal of the photo diode auto element to the photodiode array holding substrate holding the photodiode array is provided immediately below the photodiode element, Since there is a gap between the photodiode arrays, the pitch between the electrode pads cannot be made uniform over all points of the electrode pads.

  That is, for example, when a radiation detector module having a radiation detector element array of 64 columns × 24 rows is configured using two radiation detector element arrays of 32 columns × 24 rows, the 32nd and 33rd columns The distance between the electrode pads and the eyes is wider than the distance between the corresponding electrode pads in the radiation detection element array of 32 columns × 24 rows. Therefore, when using the photodiode array holding substrate as described above, only the radiation detector element array of 64 columns × 24 rows can be configured, and the radiation detector dedicated to 64 columns becomes 32 columns, It becomes impossible to correspond to 124 columns and 256 columns, and there is no extensibility.

  The same applies to the DAS chip holding substrate that holds the DAS chip.

  An object of the present invention has been made in view of the above problems, and provides an economical radiation detection apparatus and a multi-slice X-ray CT apparatus using the same by sharing parts even if the number of slices is different. There is.

The above object is achieved by the following means.
A plurality of radiation detection element arrays each including a plurality of radiation detection elements that convert incident radiation into an electrical signal; a plurality of radiation detection element arrays each having a gap between the radiation detection element arrays; A radiation detector module comprising a radiation detection element array holding substrate on which an element array is mounted and held, a radiation detector in which the radiation detector module is arranged in two dimensions, and a radiation detector that is detected by the radiation detector And a data collection system for converting the collected analog signal into a digital signal, and a position of an output terminal for taking out an output of the radiation detection element and the output terminal. Electrode pads provided on the radiation detection element array holding substrate for electrical connection to the radiation detection element array holding substrate The positions of the heads are the same, and the interval between the positions is equal to or greater than the arrangement interval of the radiation detection elements.

The following multi-slice X-ray CT is constructed using the above radiation detection apparatus.
A radiation source, a radiation detection device arranged opposite to the radiation source, a rotating disk that holds the radiation source and the radiation detection device and is driven to rotate around a subject, and is detected by the radiation detection device An image reconstructing means for reconstructing a tomographic image of the subject based on the intensity of the radiation, a plurality of radiation detecting element arrays each including a plurality of radiation detecting elements in the radiation detecting device, and the radiation A radiation detector module comprising a radiation detection element array holding substrate having a gap between the detection element arrays and mounting and holding the plurality of radiation detection element arrays, and the radiation detector modules arranged in two dimensions A configured radiation detector and a data acquisition system that collects radiation detection signals detected by the radiation detector and converts the collected analog signals into digital signals An X-ray CT apparatus using a radiation detection apparatus comprising: a position of an output terminal for taking out an output of the radiation detection element; and electrically connecting the output terminal to the radiation detection element array holding substrate The positions of the electrode pads provided on the radiation detection element array holding substrate are the same, and the interval between the positions is equal to or greater than the arrangement interval of the radiation detection elements.

  According to the present invention, even if the number of slices is different, the radiation detection element array, the radiation detection element array holding substrate, the data collection chip, and the data collection chip holding substrate can be shared. By sharing these parts, it is possible to supply a radiation detection apparatus and a multi-slice X-ray CT apparatus using the same at low cost.

Hereinafter, preferred embodiments of a radiation detection apparatus of the present invention and an X-ray CT apparatus using the same will be described in detail with reference to the accompanying drawings.
Note that components having the same function are denoted by the same reference symbols throughout the drawings for describing the embodiments of the present invention, and the repetitive description thereof will be omitted.
Further, the present invention can be used for a radiation detection apparatus using any of an indirect conversion type radiation detection element and a direct conversion type radiation detection element, and an X-ray CT apparatus using the same. An embodiment using an indirect conversion type radiation detection element will be described.

First Embodiment
FIG. 1 is a view showing a cross section of a radiation detector module of a radiation detection apparatus according to the present invention. This radiation detector module is, for example, a matrix scintillator array 13 of 32 columns in the slice direction and 24 rows in the channel direction, and a matrix array of photodiode arrays 14 each of 32 columns × 24 rows, A gap G is provided and arranged along the slice direction A on the photodiode array holding substrate 15 that holds the two photodiode arrays 14.

  The scintillator array 13 includes a plurality of scintillator elements 11. A reflection layer 12 made of a light reflecting material is provided on the side surface and the X-ray incident surface of each scintillator array 13. The light emitted from the scintillator element 11 is efficiently extracted out of the scintillator element 11 by the reflective layer 12.

  The scintillator array 13 is bonded with a photodiode array 14 having a plurality of light receiving cells (photodiode elements 16) in the same array as the scintillator array 13 with a transparent adhesive, and the photodiode array 14 A diode array holding substrate 15 is connected and mounted.

  Further, an output terminal 17 for taking out the output of the photodiode element provided on the surface opposite to the adhesive surface with the scintillator array 13, and an electrode pad 18 provided on the photodiode array holding substrate 15 are provided. It is electrically connected and mounted on the photodiode array holding substrate 15.

  The positions of the output terminal 17 and the electrode pad 18 are the same, and the interval between these positions is equal, and the output terminal 17 and the electrode pad 18 are equal on the surface in the slice direction A of the radiation detector. The cone beam radiation radiated from the radiation source divided into intervals is arranged at a position that coincides with the spread angle (cone angle) pitch in the column direction, and the interval between the positions is equal to or greater than the arrangement interval of the radiation detection elements.

  For example, when the pitch between the output terminal 17 and the electrode pad 18 is 1.0 mm in both the channel direction and the slice direction, the scintillator element 11 and the photodiode element 16 have a single scintillator array and photodiode array in the channel direction. Therefore, it is not necessary to provide a gap between the scintillator array and the photodiode array. However, since it is necessary to provide a gap between the scintillator array and the photodiode array with respect to the slice direction, the pitch of the scintillator element 11 and the photodiode element 16 is set to, for example, 0.997 mm, and the positions of the output terminal 17 and the electrode pad 18 are set. The cone beam radiation is made to coincide with the spread angle (cone angle) pitch in the column direction.

  As a result, a gap G of 0.096 mm (= 32 rows × 0.003 mm) can be provided between the photodiode arrays 14, facilitating the assembly of the radiation detector, and the spacing between the output terminals 17 and between the electrode pads 18. Since the interval is uniform over all points on the photodiode array holding substrate, the photodiode array can be mounted at an arbitrary position.

  Therefore, as shown in FIG. 2, it is also possible to configure a radiation detector for 32 slices in which only one radiation detector element array for 32 columns is mounted while being the same photodiode array holding substrate. As described above, it is also possible to configure a radiation detector for 64 slices in which two radiation detector element arrays for 32 columns are mounted. That is, the radiation detection element array composed of the scintillator array and the photodiode array and the radiation detection element array holding substrate on which the radiation detection element array is mounted can be shared for 32 slices and 64 slices.

  The radiation detector according to the first embodiment of the present invention is configured by arranging a plurality of radiation detector modules configured as described above in an arc shape centered on the focal point of a radiation source.

  In the first embodiment, the photo die auto array has a light receiving surface on the adhesive surface side with the scintillator array, and an example using a through electrode type in which an output terminal is provided on the opposite surface is given. The present invention is not limited to this, and can also be applied to the case of using a photodiode array of another type such as a back-illuminated type in which a light receiving surface is provided on the opposite side of the adhesive surface with the scintillator array.

  Also, in FIG. 1 and FIG. 2, the position of the electrode pad in order to provide the gap G, that is, the spread in the column direction of cone beam radiation emitted from the radiation source that divides the surface of the radiation detector in the slice direction at equal intervals, etc. Although the interval angle position and the radiation detection element position are misaligned, the detection error due to this misalignment can be corrected by correcting the position information of the radiation detection element pitch between the radiation detection element arrays.

  It was experimentally confirmed that the positional information correction by the deviation can be performed by setting the radiation detection element at the end of the radiation detection element array where the deviation amount is maximum within 20% of the equally spaced angular pitch. Therefore, in the case of the first embodiment, the radiation detection element at the end of the radiation detection element array has a deviation of 0.2 mm or less, and the radiation detection element pitch is 0.9875 mm or more.

  Next, the operation of the radiation detector using the radiation detector module shown in FIG. 1 will be described. Radiation incident from the direction of the arrow in FIG. 1 is absorbed by the scintillator element 11 and converted into visible light. The visible light is guided to the photodiode element 16 while being reflected by the reflecting material 12, and generates an electrical signal corresponding to the emission intensity. The generated electric signal is guided to the electrode pad 18 of the photodiode array holding substrate 15 through the output terminal 17.

  The radiation detector modules operating in this way are arranged in an arc shape centered on the focal point of a radiation source (e.g., an X-ray tube), and the analog electrical signals of the electrode pads 18 of the plurality of photodiode array holding substrates 15 are The data is transmitted to a data collection system DAS (not shown) and converted into a digital signal.

According to the first embodiment, the positions of the output terminal 17 and the electrode pad 18 are the same, and the interval between the positions is equal to or greater than the arrangement interval of the radiation detection elements. The photodiode array holding substrate can be used for various multi-slice radiation detectors.
Further, the difference between the spread angle direction angular position of the cone beam radiation emitted from the radiation source that divides the plane in the slice direction of the radiation detector at equal intervals and the position of the radiation detection element is the maximum. In the radiation detection element at the end of the radiation detection element array, the radiation detection error due to the deviation can be corrected by making it within 20% of the equally spaced angular pitch. It becomes possible to assemble.

  Furthermore, since the output terminals and electrode pads of the photodiode array are uniform over all points on the photodiode array holding substrate, the photodiode array can be mounted at an arbitrary position.

  As a result, the number of photodiode arrays provided on the photodiode array holding substrate can be made variable, and it is possible to cope with multi-slice radiation detectors having various slice numbers.

<< Second Embodiment >>
In the multi-slice X-ray CT apparatus, analog X-ray detection signals, which are the outputs of a plurality of radiation detection elements detected by the radiation detector of the first embodiment, are taken into a data acquisition system DAS (Data Acquisition System) And converted to a digital signal.

  The DAS includes an AD conversion circuit composed of a DAS chip or the like in which an integrator, a current / voltage converter, an analog / digital converter, and the like for a plurality of radiation detector elements are integrated, and a control signal. It is configured by a control circuit including a circuit for inputting and a power supply circuit.

  3 shows the radiation detector module 45 of 64 columns × 24 rows shown in FIG. 1 and 24 64-channel input DAS chips 42 from 42a to 42x that collect output from the module and convert it into digital signals. This is an example in which the AD conversion circuit 46 and the control circuit (not shown) provided are combined to constitute a 64-row multi-slice radiation detection apparatus.

  This 64-row multi-slice radiation detection apparatus is configured such that the electrode pad 18 of the photodiode array holding substrate 15 and the 24 DAS chips 42 mounted on the DAS chip holding substrate 41 are connected by a connection line 43. A digital radiation detection signal is output from an output terminal (not shown) provided on the chip holding substrate 41 to a control circuit (not shown). The control circuit collectively outputs digital signals from the plurality of AD conversion circuits as one output signal.

  In the radiation detection apparatus configured as described above, when the multi-slice radiation detection apparatus of 32 columns is used, the radiation detector module of 32 columns × 24 rows shown in FIG. 2 is used as the radiation detector module. The module output is input to 12 DAS chips 42a to 42l.

  That is, a radiation detector module of 32 columns × 24 rows is mounted in the center of the photodiode array holding substrate 15, and the 12 DAS chips 42a to 42l are used, and the remaining 42m to 42x DAS chips are not used.

  Switching between the 64 column and 32 column DAS chips is performed by a switching signal from 44 DAS chip switching means.

  With this configuration, the DAS chip and the DAS chip holding substrate can be shared for 64 rows and 32 rows.

  In the case of the 32-row multi-slice type, unused DAS chips (42m to 42x) may be removed. In this case, in addition to using the DAS chip holding substrate as a common component, the cost can be reduced by reducing the number of DAS chips.

  According to the second embodiment, since the number of DAS chips can be varied according to the number of slices using the switching signal from the DAS chip switching means, it becomes possible to share the DAS chip and the DAS chip holding substrate. These can be used for various multi-slice radiation detection apparatuses.

<< Third Embodiment >>
FIG. 4 is a diagram showing an overall configuration of an X-ray CT apparatus to which the radiation detection apparatus according to the present invention is applied. Since X-rays are used as radiation in the X-ray CT apparatus, in the following description, the radiation detection apparatus is referred to as an X-ray detection apparatus.

  The X-ray CT apparatus shown in FIG. 4 collects transmitted X-ray data of the subject by irradiating the subject with X-rays, and obtains a tomographic image by reconstructing the collected X-ray data. A scanner gantry 310 that irradiates a subject with X-rays and collects X-ray data transmitted through the subject, a bed with a movable top plate (not shown) on which the subject is placed, and various operations An image reconstruction device (image reconstruction means) 320 that performs reconstruction calculation processing using the collected X-ray data and performs CT image reconstruction, and a CT image reconstructed by the image reconstruction device 320 And a display device 330 having an operation unit for operating the X-ray CT apparatus, and a system controller 340 for controlling the entire system by an operation signal from the operation unit.

  The scanner gantry unit 310 includes a rotating disk 311 provided with an opening 314 into which a subject is carried, an X-ray tube (radiation source) 312 mounted on the rotating disk 311, and the X-ray tube 312. A collimator 313 that controls the radiation direction of the X-ray flux from the X-ray tube 312, an X-ray detector 315 mounted on the rotating disk 311 facing the X-ray tube 312, and an X-ray detected by the X-ray detector 315 A data collection system 316 that collects data, a scan control device 317 that controls the rotation of the rotating disk 311 and the width of the X-ray bundle, etc., and an unillustrated X that controls the X-ray dose emitted from the X-ray tube 312 And a line high voltage device (consisting of an X-ray control unit and a high voltage generation unit).

  The X-ray tube 312 has two directions: a channel direction (direction perpendicular to the rotation axis of the rotating disk 311) and a slice direction (direction parallel to the rotation axis of the rotating disk 311 (direction perpendicular to the paper surface)). Generates so-called cone beam X-rays.

  The data collection system 316 is the data collection system according to the second embodiment, and amplifies the signal detected by the X-ray detector 315, converts it into a digital value, and transmits it to the image reconstruction unit 320. To do.

  The image reconstruction unit 320 includes a reconstruction calculation unit 321 that performs a CT image reconstruction by calculating the measurement data S1 collected by the data collection system 316, and a CT image reconstructed by the reconstruction calculation unit 321. An image information adding unit 322 for adding information such as a subject's name, examination date and time, and examination conditions input from the operation unit of the display device 330 to the data, and CT image data with the image information added to the display device And a display control unit 323 that generates a display signal S2 for display on 330.

  The X-ray detector 315 is a two-dimensional X-ray detector that can detect two-dimensional X-ray data in the channel direction and the slice direction using the radiation detector module of the first embodiment. In this two-dimensional X-ray detector, a radiation detection element array is configured by using a plurality of radiation detection elements including a scintillator and a photodiode, and a gap is provided between the radiation detection element arrays by using the plurality of radiation detection element arrays. The radiation detector modules are arranged in an arc shape at the position of the rotating disk 311 facing the X-ray tube 312.

  The X-ray CT apparatus according to the present invention configured as described above inputs an operation command from the operation unit to the system controller 340, and a scan is executed based on the control of the system controller 340. That is, a top plate on which a subject (not shown) is placed is carried into the opening 314 of the scanner gantry unit 310, and X-rays are emitted from the X-ray tube 312 toward the subject. The emitted X-rays are focused on the imaging region of the subject by the collimator 313 and applied to the subject, and the rotating disk 311 is rotated around the subject to change the direction of X-ray irradiation. The X-ray transmitted through the subject is detected by the two-dimensional X-ray detector while changing.

  X-ray data detected by the two-dimensional X-ray detector is collected by the data acquisition system 316, converted into a digital signal S1, and input to the reconstruction calculation unit 321 of the image reconstruction device 320. Then, the reconstruction operation unit 321 reconstructs the CT image data, and the reconstructed CT image data adds information such as the subject name, the examination date and time, the examination condition, and the like by the image information addition unit 322, The display control unit 323 performs display control on the CT image data to which the image information is added, generates a display signal S2 for display on the display device 330, and displays the CT image to which the image information is added on the display device 330. .

  In the multi-slice X-ray CT apparatus configured as described above, for example, in the case of a 64-slice multi-slice X-ray CT apparatus, two sets of 32-column x 24-row radiation detection element arrays shown in FIG. 1 are mounted. Using these radiation detector modules, the output of these modules is taken out from 24 DAS chips 42a to 42x mounted on the DAS chip holding substrate 41 shown in FIG. On the other hand, in the case of a 32-column multi-slice X-ray CT apparatus, as shown in FIG. 2, a radiation detector module equipped with a set of 32 columns × 24 rows of radiation detection element arrays is used. 12 DAS chips 42a to 42l are mounted on the DAS chip holding substrate 41 shown in FIG. 3, and the outputs of the plurality of radiation detector modules are taken out from these DAS chips.

  With this configuration, the radiation of the 64-row multi-slice X-ray CT apparatus (consisting of the X-ray detector 315 and the data acquisition system 316) and the radiation of the 32-row multi-slice X-ray CT apparatus In the detection apparatus, the radiation detection element array, the photodiode array holding substrate, the data collection chip, and the data collection chip holding substrate can be shared.

  In addition, in the 128-slice multi-slice X-ray CT apparatus of 64 columns or more and the 256-slice multi-slice X-ray CT apparatus, the radiation detection is performed similarly to the 32-slice and 64-slice multi-slice X-ray CT apparatus. Equipment parts can be shared.

  As described above, by sharing the components constituting the radiation detection apparatus, the radiation detection apparatus and the multi-slice X-ray CT apparatus using the radiation detection apparatus can be supplied at low cost.

  The present invention is not limited to a radiation detection apparatus using X-rays, but can also be applied to a radiation detection apparatus such as γ-rays, a medical image diagnosis apparatus and a treatment apparatus using the same.

The figure which shows the cross section of the radiation detector module for 64 slices of the radiation detection apparatus by this invention. The figure which shows the cross section of the radiation detector module for 32 slices which carries only one radiation detector element array for 32 rows. The structural example of the radiation detection apparatus which consists of a radiation detector module for 64 slices, and a data acquisition system. The figure which shows the whole structure of the multi-slice type | mold X-ray CT apparatus with which the radiation detection apparatus by this invention is applied.

Explanation of symbols

  11 scintillator element, 12 reflective layer, 13 scintillator array, 14 photodiode array, 15 photodiode array holding substrate, 16 photodiode element, 17 output terminal of photodiode element, 18 electrode pad of photodiode array holding substrate, 41 data collection Chip holding substrate, 42 data collection chip, 43 connection line, 44 data collection chip switching means, 45 radiation detector module, 46 AD converter circuit, 310 scanner gantry, 311 rotating disk, 312 X-ray tube (radiation source), 315 X-ray detector, 316 data acquisition system, 320 image reconstruction device, 330 display device, 340 system controller, A slice direction

Claims (5)

A plurality of radiation detection element arrays each including a plurality of radiation detection elements that convert incident radiation into an electrical signal; a plurality of radiation detection element arrays each having a gap between the radiation detection element arrays; A radiation detector module comprising a radiation detection element array holding substrate for mounting and holding an element array, a radiation detector in which the radiation detector modules are arranged two-dimensionally or one-dimensionally, and the radiation detector In a radiation detection apparatus comprising: a data acquisition system that collects the radiation detection signals detected in step 1 and converts the collected analog signals into digital signals;
The position of the output terminal for extracting the output of the radiation detection element is the same as the position of the electrode pad provided on the radiation detection element array holding substrate for electrically connecting the output terminal to the radiation detection element array holding substrate. And the space | interval between the said positions is equal intervals, and is more than the arrangement | positioning space | interval of the said radiation detection element, The radiation detection apparatus characterized by the above-mentioned. The distance by which the position of the radiation detection element at the end of the adjacent radiation detection element array in the gap and the position of the electrode pad corresponding to the radiation detection element is more than 0% of the distance between the electrode pads. The radiation detection apparatus according to claim 1, wherein the radiation detection apparatus is equal to or less than%.   The data collection system includes a plurality of data collection chips that collect radiation detection signals detected by the plurality of radiation detection elements and convert the collected analog signals into digital signals, and the plurality of data collection chips. The radiation detection apparatus according to claim 1, further comprising a data collection chip variable unit that includes a data collection chip holding substrate to hold and further varies the number of operations of the data collection chip.   The radiation detection apparatus according to claim 3, wherein the data collection chip variable unit generates a data collection chip operation switching signal for switching between operation and non-operation of a plurality of data collection chips. A radiation source, a radiation detection device arranged opposite to the radiation source, a rotating disk that holds the radiation source and the radiation detection device and is driven to rotate around a subject, and is detected by the radiation detection device An image reconstructing means for reconstructing a tomographic image of the subject based on the intensity of the radiation, a plurality of radiation detecting element arrays each including a plurality of radiation detecting elements in the radiation detecting device, and the radiation A radiation detector module comprising a radiation detection element array holding substrate having a gap between the detection element arrays and mounting and holding the plurality of radiation detection element arrays, and the radiation detector module is two-dimensional or one-dimensional An array of configured radiation detectors and data for collecting the radiation detection signals detected by the radiation detectors and converting the collected analog signals into digital signals An X-ray CT apparatus using the radiation detecting device including collecting and system, and
The position of the output terminal for taking out the output of the radiation detection element is the same as the position of the electrode pad provided on the radiation detection element array holding substrate for electrically connecting the output terminal to the radiation detection element array holding substrate. The X-ray CT apparatus is characterized in that the intervals between the positions are equal and are equal to or greater than the arrangement interval of the radiation detection elements.

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