JP2000056021A - Radiation detector and nuclear medical diagnostic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a radiation detector and a nuclear medical diagnostic device capable of improving the position resolution and sensitivity on the incidence position of γ-rays by forming the detector into a recessed curved surface against a specimen, and locating a detection face near the surface of the specimen. SOLUTION: This radiation detector is constituted of a semiconductor detector array 30 provided with multiple semiconductor cells for detecting the γ-rays emitted from a specimen P and having a recessed curved surface against the specimen P and parallel collimators 31 provided along a detection face on the specimen P side of the semiconductor detector array 30. The semiconductor cells of the semiconductor detector array 30 are made of a CdTe semiconductor, and an electrode for applying a voltage to the semiconductor cells is arranged in parallel with or perpendicularly to the incidence direction of γ-rays. The detection face of the semiconductor detector array 30 is located near the specimen P to improve position resolution.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method for converting radiation such as gamma (.gamma.) Radiation emitted by a radioisotope (radioisotope, RI) injected into a subject such as a patient into one-dimensional or one-dimensional radiation. The present invention relates to a radiation detector and a nuclear medicine diagnostic apparatus for two-dimensionally detecting and obtaining an RI distribution in a subject.

[0002]

2. Description of the Related Art For example, a radioisotope (radio isotope, RI) is injected into a subject such as a patient, and radiation such as gamma rays (γ) emitted from the body is detected by a one-dimensional or two-dimensional detector. SPEC using Single Photon Emission Computed Tomography (SPECT) that displays functional distribution images such as lesions in the body, blood flow, fatty acid metabolism, etc. by acquiring RI distribution
Positron (positron) equipped with T device and multiple detectors
Is bound by electrons (negative electrons) and disappears.
2. Description of the Related Art A PET apparatus using a coincidence type positron emission computer tomography (PET) that performs imaging by simultaneously detecting gamma rays emitted in a direction of 0 ° is known. Recently, a SPECT apparatus equipped with a plurality of detectors for performing the SPECT and the coincidence-type PET has been known. These devices are generally referred to as nuclear medicine diagnostic devices.

[0003]

In the conventional SPECT apparatus, an anger-type detector which detects a gamma ray by arranging a plurality of scintillators and photomultiplier tubes (PMT) in close proximity has predominantly been used. In addition to the large scale, there was a limit to the energy resolution and the counting characteristics, so that a dramatic improvement in performance over the current level could not be expected.

On the other hand, in a coincidence-type PET apparatus, a gamma ray is 18 due to a combination of a bismuth germanium oxide (BGO) detector, a photomultiplier tube and a photodiode.
A method of performing imaging by simultaneously detecting the timing of emission in the 0 ° direction is the mainstream.

Further, recently, a nuclear medicine diagnostic apparatus using an Anger-type detector having a plurality of detectors and capable of realizing coincidence-type PET by mode switching has emerged and is becoming mainstream.

However, in any nuclear medicine diagnostic apparatus, a detector for detecting a gamma ray is mainly composed of a scintillator, and the gamma ray incident on this detector is once converted into weak light by a scintillator, and this weak light is converted. It is necessary to convert light into an electric signal using a photomultiplier or a photodiode. Therefore, the size of the nuclear medicine diagnostic apparatus has been increased, and its performance has been limited.

Therefore, attention has been paid to semiconductor detectors. Since the semiconductor detector directly converts gamma rays into electric signals, the conversion efficiency into electric signals is good, and the gamma rays can be individually detected by the semiconductor cells. Therefore, improvements in energy resolution and counting characteristics are expected.

A cadmium telluride (CdTe) based semiconductor cannot have a single crystal structure unlike sodium iodide (NaI) used in current Anger-type detectors, so that a small detector module (semiconductor type) can be used. An example in which a two-dimensional semiconductor detector is configured by closely disposing a two-dimensional array cell and a preamplifier and a read-out circuit formed below the two-dimensional array cell without protruding outside the two-dimensional array cell) There is. However, it has been difficult to reconstruct the RI image because the interconnection between the detector modules and the dead space inside each detector module become non-uniform and unique artifacts occur. In addition, in the case of such a module, only a signal processing that can be performed inside each detector module can be performed, and a plurality of semiconductors are used in a nuclear medicine diagnostic apparatus that processes high energy of 511 keV like a coincidence type PET apparatus. In the case of observing coincidence counting across cells (ie, a plurality of detector modules), signal processing becomes extremely difficult at present.

Further, in a semiconductor cell used in a semiconductor detector, it is difficult to form fine pixels as in a conventional digital gamma camera due to cost and mounting restrictions, and there is a limit in subdivision.

Incidentally, the Anger type detector is generally designed to be planar. FIG. 1 is a diagram for explaining a configuration of a conventional Anger-type flat panel detector and a positional relationship with a subject. The Anger-type flat detector shown in FIG. 1 is configured such that the parallel collimator 10 and the scintillator 11 are each planar. RI injected into subject P
The gamma ray emitted from the body is converted into light by the scintillator 11 via the parallel collimator 10, and then converted into an electric signal by a photomultiplier tube (not shown) and subjected to signal processing. In addition, since the subject P has a curved surface, the center of the anger-type flat detector shown in FIG. 1 is close to the subject P, but this flat detector becomes closer to the periphery of the subject P. Is the subject P
, The position resolution for detecting the incident position of the gamma ray generally deteriorates.

Instead of such an anger-type flat detector, it is possible to use a curved detector which is concave with respect to the subject P so that the whole is closer to the patient. FIG.
FIG. 2 is a diagram for explaining a configuration of a curved surface detector of a conventional Anger-type gamma camera and a positional relationship with a subject. Anger type gamma camera shown in Fig. 2 (manufactured by BICRON)
Is composed of two concave curved surface detectors 20a and 20b arranged to face each other across the subject P. The curved surface detectors 20a and 20b are separated from each other by a rotation radius R about the rotation center O, and are moved around the subject P along the rotation direction D1 by a drive mechanism (not shown).

The curved surface detectors 20a and 20b have the same configuration. The curved surface detector 20a includes the scintillator 2
1a, light guide 22a, and photomultiplier tube 23
, 23n, and the curved surface detector 20b includes a scintillator 21b, a light guide 22b, and photomultiplier tubes 24a,..., 24n. Each of the scintillators 21a and 21b has a cylindrical shape with a curved surface, and has a certain thickness t1 when viewed from the rotation center O. The detection of the incident position of the gamma ray is performed by the photomultiplier tubes 23a,..., 23n, 24a,.
24n.

The curved surface detector 20 constructed as described above
Regarding the gamma rays incident on the central portions of the scintillators 21a and 21b in FIGS. 20a and 20b, since the shift of the incident positions is small, an accurate incident position can be calculated by the photomultiplier tube. However, in SPECT, for example, a parallel collimator (not shown) is provided with scintillators 21a,
In the case where the scintillators 21a and 21b are respectively installed on the subject side of 1b to detect parallel gamma rays, the scintillators 21a and 21b are configured to have a constant thickness t1 in a cylindrical shape when viewed from the rotation center O, and therefore, the curved surface detection is performed. Gamma rays are emitted from the scintillators 21a and 21b from the center to the periphery of the vessels 20a and 20b.
The distance that passes through increases. Therefore, DOI (Dept
The influence of h of interaction increases, and a position resolution error Δ occurs in the scintillators 21a and 21b depending on the position where the gamma ray is absorbed, and the accuracy of the calculated position resolution is degraded. For this reason, the curved surface detectors 20a and 20b are close to the subject P in their peripheral portions, but the positional resolution is not improved. Therefore, for SPECT, the advantage that the peripheral portions of the detectors are close to the subject should be fully utilized. Can not. In addition, a difference in sensitivity occurs depending on the incident position of the gamma ray (the sensitivity is improved in the peripheral portion), and it is difficult to improve the sensitivity in the central portion where the sensitivity is originally desired to be improved.

In the coincidence type PET, the position of the positron PO (511 keV) along a line extending perpendicularly to the curved surfaces of the scintillators 21a and 21b from the rotation center O can be ideally calculated. However, as described above, when detecting a parallel gamma ray by installing a parallel collimator, the scintillators 21a and 21b are configured to have a certain thickness t1 in a cylindrical shape when viewed from the rotation center O. The distance of the gamma rays originating from the positron PO passing through the scintillators 21a and 21b increases toward the peripheral portion, and the influence of the DOI increases. As a result, the position resolution is deteriorated, which causes deterioration in the image quality of the reconstructed RI image.

In particular, when the thickness t1 of the scintillators 21a and 21b is large, an incident position where the influence of the DOI becomes extremely large occurs depending on the incident angle of the gamma ray caused by the positron PO. For this reason, when using a gamma camera in which two detectors are arranged facing each other, the solid angle θ1 becomes small unless these two detectors are separated from each other by a predetermined distance or more. Therefore, sufficient image quality cannot be obtained. Therefore, although the solid angle of the curved surface detector is originally larger than that of the planar detector, the coincidence solid angle θ1 for detecting gamma rays in PET, which is expected of the curved surface detector, is set to be larger than expected. It could not be set large, and there was a limit in improving sensitivity.

Further, for the above-mentioned reason, even in the case of the fan beam SPECT having a short focal length, the deterioration of the position resolution becomes large in the peripheral portion of the detector.

Furthermore, SPECT and simultaneous counting type PE
When it is desired to share T, it has been difficult to obtain a greater merit than when both are used together and a flat detector is used.

SUMMARY OF THE INVENTION The present invention has been made in view of the above circumstances, and an object of the present invention is to form a concave shape with respect to a subject so that a detection surface is brought close to the surface of the subject, and a position related to a gamma ray incident position is provided. An object of the present invention is to provide a radiation detector and a nuclear medicine diagnostic apparatus capable of improving resolution and sensitivity.

[0019]

In order to solve the above-mentioned problems, a radiation detector according to the present invention is arranged in a concave shape with respect to a subject and in parallel with each other. A plurality of semiconductor cells for detecting the radiation, and a voltage application electrode for applying a voltage to the semiconductor cells.

In the radiation detector according to the first aspect of the present invention, in the second aspect of the present invention, the plurality of semiconductor cells are arranged such that the positions of the incident surfaces in the incident direction of the radiation are continuously shifted. By doing so, a concave shape is formed along the surface of the subject.

[0021] In the radiation detector according to the first aspect of the present invention, the invention according to the third aspect is characterized in that, in the plurality of semiconductor cells, an incident surface in the incident direction of the radiation is set for every two or more semiconductor cells. By continuously displacing the positions, a concave shape is formed along the surface of the subject.

In the radiation detector according to the first aspect of the present invention, the invention according to the fourth aspect is characterized in that the plurality of semiconductor cells are arranged in a matrix.

In the radiation detector according to the first aspect of the present invention, the invention according to the fifth aspect is characterized in that the thickness of the plurality of semiconductor cells in the absorption direction of the incident radiation is all constant. I do.

[0024] In the radiation detector according to the first aspect of the present invention, the invention according to the sixth aspect is characterized in that the thickness in the radiation absorption direction is different between a central portion of the radiation detector and a peripheral portion thereof. I do.

In the radiation detector according to the sixth aspect, the invention according to the seventh aspect is characterized in that the thickness in the radiation absorption direction is larger at the peripheral portion than at the central portion of the radiation detector. Features.

According to another aspect of the present invention, there is provided a radiation detector according to the present invention, wherein the plurality of semiconductor cells are arranged in parallel, and each of the plurality of semiconductor cells detects radiation from a subject. A semiconductor detector array having a voltage application electrode for applying a voltage to the subject, and a detection surface formed in a concave shape with respect to the subject, and provided along the detection surface of the semiconductor detector array And a parallel collimator.

[0027] In the radiation detector according to the eighth aspect of the present invention, the radiation detector according to the ninth aspect is arranged such that the size of the detection surface is on the rear side of the semiconductor detection array opposite to the detection surface. A processing circuit that is formed so as not to protrude from the range and processes a detection signal from each semiconductor cell;
The processing circuit is formed integrally with the semiconductor detector array.

According to another aspect of the present invention, there is provided a radiation detector according to the present invention, comprising: a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject; And a voltage application electrode for applying a voltage to the semiconductor device, and two semiconductor detector arrays each having a detection surface formed in a concave shape with respect to the subject.
The two semiconductor detector arrays are opposed to each other with the subject interposed therebetween.

In order to solve the above-mentioned problems, a radiation detector according to the present invention is provided with a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject, and And a voltage application electrode for applying a voltage to the semiconductor device, and two semiconductor detector arrays each having a detection surface formed in a concave shape with respect to the subject.
The two semiconductor detector arrays are set at an arbitrary angle with respect to the subject.

According to another aspect of the present invention, there is provided a radiation detector, comprising: a plurality of semiconductor cells each arranged in parallel to detect radiation from a subject; A voltage application electrode for applying a voltage to the object, comprising three or more semiconductor detector arrays having a detection surface formed in a concave shape with respect to the subject, and the three or more semiconductor detector arrays Is set so as to sandwich the subject.

In order to solve the above-mentioned problems, a radiation detector according to the present invention is provided with a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject, and A voltage application electrode for applying a voltage to the object, comprising a plurality of semiconductor detector arrays having a detection surface formed in a concave shape with respect to the subject, wherein the plurality of semiconductor detector arrays are one-dimensional or It is characterized by being arranged two-dimensionally.

In the radiation detector according to any one of the eighth to thirteenth aspects, the invention according to the fourteenth aspect is characterized in that the semiconductor detector array has a thickness other than the semiconductor cell part in a predetermined direction of the detection surface. Is formed so as to be approximately 1/10 or less of the thickness of the semiconductor cell portion.

In order to solve the above-mentioned problem, a radiation detector according to the present invention is provided with a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject, and A voltage applying electrode for applying a voltage to the object, at least one semiconductor detector array having a concave detection surface with respect to the subject, and And one or more fan beam collimators having a fixed focal point.

According to another aspect of the present invention, there is provided a radiation detector according to the present invention, wherein a plurality of semiconductor cells are arranged in parallel, and each of the semiconductor cells detects radiation from a subject. A voltage application electrode for applying a voltage to the object, a detection surface is formed in a concave shape with respect to the subject, and two semiconductor detector arrays that are opposed to each other; A fan beam collimator provided along the detection surface and having a different focal position.

According to another aspect of the present invention, there is provided a radiation detector, comprising: a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject; Two semiconductor detector arrays having a voltage application electrode for applying a voltage to the object, a detection surface formed in a concave shape with respect to the subject, and installed at an arbitrary angle; and the two semiconductor detectors A fan beam collimator provided along the detection surface of the array and having a constant focal point.

According to another aspect of the present invention, there is provided a radiation detector, comprising: a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject; Two semiconductor detector arrays having a voltage application electrode for applying a voltage to the object, a detection surface formed in a concave shape with respect to the subject, and installed at an arbitrary angle; and the two semiconductor detectors A fan beam collimator provided along the detection surface of the array and having a different focal position.

According to another aspect of the present invention, there is provided a radiation detector according to claim 19, wherein each of the plurality of semiconductor cells is arranged in parallel and detects a radiation from a subject. A voltage application electrode for applying a voltage to the semiconductor device, two semiconductor detector arrays each having a detection surface formed in a concave shape with respect to the subject and installed at an arbitrary position, and the two semiconductor detectors A fan beam collimator provided along the detection surface of the array and having a constant focal point.

In order to solve the above-mentioned problems, a radiation detector according to the present invention is provided with a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject, and A voltage application electrode for applying a voltage to the test object, a detection surface is formed in a concave shape with respect to the subject, two semiconductor detector arrays installed at arbitrary positions, and the semiconductor detector array A fan beam collimator provided along the detection surface and having a different focal position.

According to a twenty-first aspect of the present invention, there is provided a radiation detector according to the twenty-first aspect, wherein a plurality of semiconductor cells are arranged in parallel, and each of the semiconductor cells detects radiation from a subject. Three or more semiconductor detector arrays having a voltage application electrode for applying a voltage to the object, and having a detection surface formed in a concave shape with respect to the subject and being installed, and the three or more semiconductor detectors And a fan beam collimator provided along the detection surface of the detector array and having different focal positions.

In order to solve the above-mentioned problem, the radiation detector according to the invention of claim 22 has a concave shape with respect to the subject,
And two radiation detector arrays respectively arranged in parallel and each having a plurality of detection elements for detecting radiation from the subject, wherein the two radiation detector arrays have respective detection surfaces of the subject. It is characterized by being arranged opposite to the subject so as to be formed along the surface.

In the radiation detector according to the twenty-second aspect, the invention according to the twenty-third aspect further comprises collimators attached to the detection surfaces of the two radiation detector arrays, respectively. The detector array has a concave detection surface on which a cylindrical structure having a diameter of 24 cm or less can be arranged in a space formed by the opposed arrangement, and a radiation incident surface of the collimator and a surface of the cylindrical structure. Is within the range of 0.5 cm to 2 cm.

In the radiation detector according to the twenty-third aspect of the present invention, the radiation detector array according to the twenty-fourth aspect is characterized in that each of the radiation detector arrays is arranged closely at each end. .

To solve the above problem, a radiation detector according to the twenty-fifth aspect of the present invention provides a radiation detector that
And a plurality of detection elements for detecting radiation from the subject, each being arranged in parallel.

According to another aspect of the present invention, there is provided a radiation detector including two curved detector modules each having a plurality of detection elements for detecting radiation arranged in parallel. The two detector modules are combined to form a concave shape with respect to the subject.

[0045] In the radiation detector according to the twenty-fifth or twenty-sixth aspect, the invention according to the twenty-seventh aspect is characterized in that the plurality of detection elements are constituted by a semiconductor or a scintillator.

In the radiation detector according to the twenty-fifth or twenty-sixth aspect, the invention according to the twenty-eighth aspect is characterized in that the plurality of detection elements are arranged so that the positions of the incident surfaces in the incident direction of the radiation are shifted. It is characterized by having.

The radiation detector according to the twenty-fifth aspect of the present invention is the radiation detector according to the twenty-ninth aspect, further comprising a detector module in which the plurality of detection elements are arranged, and the detector module is provided at both ends of the detector module. Is characterized in that a portion that does not contribute to the detection of radiation is provided.

The radiation detector according to the twenty-sixth aspect of the present invention is the radiation detector according to the thirty-second aspect, wherein the two detector modules are connected to each other by connecting one end thereof, and are respectively connected to the other end. The part is provided with a part that does not contribute to the detection of radiation.

[0049] In the radiation detector according to the twenty-fifth or twenty-sixth aspect, the invention according to the thirty-first aspect is characterized in that the plurality of detection elements are arranged in a matrix.

In order to solve the above-mentioned problem, the radiation detector according to the invention of claim 32 has a concave shape with respect to the subject,
And a plurality of detector modules each arranged in parallel, each having a plurality of detection elements for detecting radiation from the subject, wherein each of the detector modules is arranged in a predetermined direction, and a step portion And a protruding portion, and the protruding portion is mounted on a step portion of an adjacent detector module and combined.

In the radiation detector according to the present invention, the detector module has a flexible substrate electrically connected to the plurality of detection elements. In addition, a processing circuit for processing a detection signal detected by each of the detection elements can be connected to the flexible substrate.

According to a thirty-fourth aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject. The semiconductor device is characterized by comprising a plurality of semiconductor cells arranged in a concave shape with respect to a specimen and in parallel with each other, and a voltage application electrode for applying a voltage to the semiconductor cells.

[0053] In the nuclear medicine diagnostic apparatus according to the invention described in claim 34, in the invention described in claim 35, the plurality of semiconductor cells continuously shift the position of the incident surface in the incident direction of the radiation. The arrangement is characterized in that a concave shape is formed along the surface of the subject.

In the nuclear medicine diagnostic apparatus according to the present invention, the radiation is incident on the plurality of semiconductor cells in the incident direction of the radiation for each set of two or more semiconductor cells. It is characterized in that a concave shape is formed along the surface of the subject by arranging the surfaces continuously shifted.

[0055] In the nuclear medicine diagnostic apparatus according to the invention described in claim 34, the invention described in claim 37 is characterized in that the plurality of semiconductor cells are arranged in a matrix.

In the nuclear medicine diagnostic apparatus according to the invention described in claim 34, the invention described in claim 38 is characterized in that the thickness of the plurality of semiconductor cells in the absorption direction of incident radiation is all constant. And

In the nuclear medicine diagnostic apparatus according to the thirty-fourth aspect, the thirty-ninth aspect of the present invention is characterized in that the thickness of the radiation detector in the radiation absorption direction is different between the central part and the peripheral part of the radiation detector. And

In the nuclear medicine diagnostic apparatus according to the present invention, the thickness in the radiation absorption direction is larger at the peripheral portion than at the central portion of the radiation detector. It is characterized by.

In order to solve the above problem, an invention according to claim 41 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is A plurality of semiconductor cells arranged in parallel, having a voltage application electrode for applying a voltage to the semiconductor cell, a semiconductor detector array in which the detection surface is formed in a concave shape with respect to the subject, A parallel collimator provided along a detection surface of the semiconductor detector array.

[0060] In the nuclear medicine diagnostic apparatus according to the present invention, the size of the detection surface may be larger than the size of the detection surface on the back side of the semiconductor detection array opposite to the detection surface. And a processing circuit for processing a detection signal from each semiconductor cell. The processing circuit is formed integrally with the semiconductor detector array.

In order to solve the above-mentioned problem, an invention according to claim 43 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors Two semiconductor detector arrays each having a plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cells, wherein a detection surface is formed in a concave shape with respect to the subject. Wherein the two semiconductor detector arrays are opposed to each other with the subject interposed therebetween.

In order to solve the above-mentioned problem, the invention according to claim 44 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is Two semiconductor detector arrays each having a plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cells, wherein a detection surface is formed in a concave shape with respect to the subject. Wherein the two semiconductor detector arrays are arranged at an arbitrary angle with the subject interposed therebetween.

In order to solve the above problem, an invention according to claim 45 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is Three or more semiconductor detection devices having a plurality of semiconductor cells arranged in parallel and a voltage application electrode for applying a voltage to the semiconductor cells, wherein a detection surface is formed in a concave shape with respect to the subject. Device array,
The three or more semiconductor detector arrays are provided so as to sandwich the subject.

In order to solve the above-mentioned problem, the invention according to claim 46 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is A plurality of semiconductor detector arrays each having a plurality of semiconductor cells arranged in parallel and a voltage application electrode for applying a voltage to the semiconductor cells, wherein a detection surface is formed in a concave shape with respect to the subject. Wherein the plurality of semiconductor detector arrays are arranged one-dimensionally or two-dimensionally.

In the nuclear medicine diagnostic apparatus according to any one of claims 41 to 46, the invention according to claim 47 is characterized in that the semiconductor detector array has a portion other than the semiconductor cell portion in a predetermined direction of the detection surface. It is characterized in that the thickness is formed to be approximately 1/10 or less of the thickness of the semiconductor cell portion.

According to another aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors One or more semiconductor detectors having a plurality of semiconductor cells arranged in parallel and a voltage application electrode for applying a voltage to the semiconductor cells, wherein a detection surface is formed in a concave shape with respect to the subject. A detector array, and one or more fan beam collimators provided along a detection surface of the semiconductor detector array and having a constant focal point.

In order to solve the above problem, an invention according to claim 49 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is It has a plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cell, the detection surface is formed in a concave shape with respect to the subject, and the two A semiconductor detector array is provided, and a fan beam collimator provided along a detection surface of each of the two semiconductor detector arrays and having a different focus position is provided.

In order to solve the above-mentioned problem, an invention according to claim 50 is a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is It has a plurality of semiconductor cells arranged in parallel and a voltage application electrode for applying a voltage to the semiconductor cells, the detection surface is formed in a concave shape with respect to the subject, and is installed at an arbitrary angle. It is characterized by comprising two semiconductor detector arrays and a fan beam collimator provided along a detection surface of each of the two semiconductor detector arrays and having a fixed focal point.

In order to solve the above-mentioned problem, an invention according to claim 51 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is It has a plurality of semiconductor cells arranged in parallel and a voltage application electrode for applying a voltage to the semiconductor cells, the detection surface is formed in a concave shape with respect to the subject, and is installed at an arbitrary angle. It is characterized by comprising two semiconductor detector arrays and fan beam collimators provided respectively along the detection surfaces of the two semiconductor detector arrays and having different focal positions.

According to a second aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors comprises: It has a plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cells, the detection surface is formed in a concave shape with respect to the subject, and is installed at an arbitrary position. It is characterized by comprising two semiconductor detector arrays and a fan beam collimator provided along a detection surface of each of the two semiconductor detector arrays and having a fixed focal point.

In order to solve the above problem, an invention according to claim 53 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein each of the radiation detectors is It has a plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cells, the detection surface is formed in a concave shape with respect to the subject, and is installed at an arbitrary position. It is characterized by comprising two semiconductor detector arrays and fan beam collimators provided respectively along the detection surfaces of the two semiconductor detector arrays and having different focal positions.

According to a fifty-fourth aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject. A plurality of semiconductor cells arranged in parallel, and a voltage application electrode for applying a voltage to the semiconductor cells, three or more of which are arranged such that a detection surface is formed in a concave shape with respect to the subject; And a fan beam collimator provided along a detection surface of the three or more semiconductor detector arrays and having different focal positions.

According to a fifty-fifth aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject. It comprises two radiation detector arrays each having a plurality of detection elements arranged in parallel with each other in a concave shape with respect to the specimen, and the two radiation detector arrays each have a detection surface on the surface of the subject. It is characterized by being arranged to face each other across the subject so as to be formed along.

The nuclear medicine diagnostic apparatus according to claim 55, wherein the invention according to claim 56 further comprises collimators attached to the detection surfaces of the two radiation detector arrays, respectively. The detector array has a space of 24 cm in the space formed by its opposing arrangement.
Each having a concave detection surface on which a cylindrical structure having the following diameter can be arranged, the shortest distance between the radiation incident surface of the collimator and the surface of the cylindrical structure is 0.5 cm.
From 2 to 2 cm.

In the nuclear medicine diagnostic apparatus according to the present invention, the radiation detector array is characterized in that each end of the radiation detector array is closely arranged. I do.

According to another aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject. And a plurality of detecting elements arranged in a concave shape with respect to each other and in parallel with each other.

In order to solve the above problem, an invention according to claim 59 is a nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detectors are arranged in parallel. It is characterized by comprising two curved detector modules each having a plurality of arranged detection elements, and combining the two detector modules to form a concave shape with respect to the subject.

[0078] In the nuclear medicine diagnostic apparatus according to claim 58 or 59, the invention according to claim 60 is characterized in that:
The plurality of detection elements are constituted by a semiconductor or a scintillator.

In the nuclear medicine diagnostic apparatus according to the invention described in claim 58 or 59, the invention described in claim 61 is characterized in that:
The plurality of detection elements are arranged so as to be shifted from each other in a direction of incidence of radiation.

In the nuclear medicine diagnostic apparatus according to the invention described in claim 58, the invention described in claim 62 has a detector module in which the plurality of detection elements are arranged, and both ends of the detector module. Is provided with a portion that does not contribute to the detection of radiation.

In the nuclear medicine diagnostic apparatus according to claim 59, the invention according to claim 63 is characterized in that the two detector modules are combined by connecting one end of each of the two detector modules, and each of the other detector modules is connected to the other. The end is provided with a portion that does not contribute to the detection of radiation.

[0082] In the nuclear medicine diagnostic apparatus according to claim 58 or 59, the invention according to claim 64 is characterized in that:
The plurality of detection elements are arranged in a matrix.

According to another aspect of the present invention, there is provided a nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector includes the radiation detector. A plurality of detector modules each having a plurality of detection elements arranged in a concave shape with respect to the sample and in parallel with each other, wherein each of the detector modules is arranged in a predetermined direction, and includes a step portion and a projecting portion. The protruding portion is mounted on a step portion of an adjacent detector module and is combined.

In the nuclear medicine diagnostic apparatus according to the above aspect, the detector module may further comprise a flexible substrate electrically connected to the plurality of detection elements. And a processing circuit for processing a detection signal detected by each of the detection elements can be connected to the flexible substrate.

[0085]

Embodiments of the present invention will be described below with reference to the drawings.

FIG. 3 is a diagram showing the configuration of the radiation detector according to the embodiment of the present invention and the positional relationship with the subject. FIG.
The radiation detector used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention is used as a detection element for detecting radiation such as gamma (γ) rays emitted from a subject P such as a patient. Comprising a plurality of semiconductor cells,
Semiconductor detector array 3 concave and curved with respect to subject P
0 and a parallel collimator 31 provided on the object side of the semiconductor detector array 30 along the detection surface. Note that the parallel collimator 31 is used to pass only gamma rays incident on the subject P from a vertical direction and guide the gamma rays to the semiconductor detector array 30.

Each semiconductor cell of the semiconductor detector array 30 is made of a cadmium telluride (CdTe) -based semiconductor. In this semiconductor, a voltage application electrode and a signal extraction electrode are arranged in a direction (parallel direction) horizontal to a direction in which gamma rays are incident. The voltage application electrode is used to apply a high voltage to the semiconductor, and the signal extraction electrode is used to extract a detection signal from the semiconductor. The semiconductor cells are arranged at equal intervals so that the longitudinal direction thereof coincides with the gamma ray incident direction. In such a semiconductor, a voltage application electrode and a signal extraction electrode can be arranged in a direction perpendicular to a direction in which gamma rays are incident.

The semiconductor detector array 30 employs a structure in which the thickness of the electrode portion (voltage application electrode and signal extraction electrode) on the detection surface is smaller than the thickness of the semiconductor cell portion, and the dead zone (gamma ray detection). The electrode portion, which does not contribute to the detection, is formed so as to be approximately 1/10 or less of the semiconductor cell portion, which is the sensitive zone (contributes to gamma ray detection). The semiconductor detector array 30 thus formed is arranged in a concave and curved surface.

In order to make the detection surface of the radiation detector as close as possible to the subject P at any position, depending on the shape of the subject P, the width of the observation field of view of the radiation detector should be 50 cm to 60 cm. It is preferable that the bending is within the range, and the degree of bending is within the range of 10 cm to 12 cm. Accordingly, the position resolution can be greatly improved because the peripheral portion of the radiation detector is also close to the subject P.

Recently, there is a case where a two-dimensional detector is constructed by closely arranging monolithic module detectors. In this case, a radiation detector as shown in FIG. 3 must be constructed. It is difficult.

In the embodiment of the present invention, the electrodes (voltage application electrodes and signal extraction electrodes) of the semiconductor detector array 30 are provided horizontally with respect to the gamma ray incidence direction. Since a plurality of semiconductor cells can be arranged so as to have the same thickness in the same direction (gamma ray absorption direction) in the same direction as when the parallel collimator is installed in the conventional Anger-type gamma camera shown in FIG. There is no difference in detection sensitivity depending on the incident position.

In the embodiment of the present invention, the radiation detector is not limited to the shape shown in FIG. As shown in FIG. 4, for example, a concave radiation detector having three planes and having a semiconductor detector array 35 and a parallel collimator 36 may be used. That is, in the present invention, it is desirable to use a radiation detector having a detection surface as close as possible to the surface of the subject P.

As shown in FIG. 5, in order to cope with the case where the incident direction of the gamma rays is obliquely inclined, a concave slant (sla) in which each semiconductor cell is inclined and arranged in parallel.
It is also possible to use a radiation detector 37 of the (nt) type. By using such a radiation detector 37, the detection surface can be brought as close as possible to the subject P. It is also possible to arrange a parallel collimator (not shown), which is configured to be inclined similarly to each semiconductor cell, on the detection surface side of the radiation detector 37.

FIG. 6 is a diagram showing a case where a fan beam collimator is installed in two radiation detectors used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention, and a positional relationship with a subject. As shown in FIG. 6, two concave and curved radiation detectors 40 and 41 according to the embodiment of the present invention are opposed to each other to sandwich an organ (for example, a head H) having a diameter of about 20 cm of a subject P. It is installed in close proximity. Radiation detector 4
Reference numerals 0 and 41 denote concave and curved semiconductor detector arrays 30a and 30b for detecting comma lines, and semiconductor detector arrays 3 and 3, respectively.
0a, 30b, a short-range focus fan beam collimator 32a disposed along the detection surface on the subject side,
32b. In FIG. 6, O1
Indicates the focus of the fan beam collimator 32b, and O2 indicates the focus of the fan beam collimator 32a. The semiconductor detector arrays 30a and 30b have the same configuration as the semiconductor detector array 30 shown in FIG.

By arranging the radiation detector according to the embodiment of the present invention as shown in FIG. 6, it is possible to enlarge the observation field of view, which cannot be realized with the fan beam system of the conventional Anger-type gamma camera, and to improve the object P. Approach to the radiation detector and enlargement of the solid angle for simultaneous detection of the detected gamma rays, and S
It is possible to greatly improve the image quality of the PECT image.

Further, even if the long distance focus fan beam collimators, which cover the whole body of the subject P in the radiation detectors 40 and 41, are opposed to each other and the facing distance is lengthened, the observation field of view can be enlarged and covered. The proximity of the radiation detector to the sample and the increase in the solid angle of simultaneous detection of the detected gamma rays can be achieved, and the image quality of whole body SPECT images, etc., is higher than the image quality obtained simply by the proximity of the radiation detector to the subject. Can be expected to be improved.

As described above, the radiation detector 4
In order to make the detection planes 0 and 41 as close as possible to the subject P at any position, the width of the observation field of view of the radiation detectors 40 and 41 is set within a range of 50 cm to 60 cm, and the degree of bending is set within a range of 10 cm to 12 cm. And inside. Thereby, since the peripheral portions of the radiation detectors 40 and 41 are also close to the subject P, it is possible to greatly improve the positional resolution. Further, the radiation detectors 40 and 41 can be arranged sufficiently close to small organs such as the head H.

FIG. 6 shows radiation detectors 40 and 41 whose respective ends are connected to each other and opposed to each other. However, the present invention is not limited to such an arrangement. For example, it is possible to arrange the radiation detectors 40 and 41 apart from each other without connecting them. Also,
The respective ends of the radiation detectors 40 and 41 are not connected but may be arranged as close as possible.

Further, when a collimator (not shown) is attached to the detection surface of each of the radiation detectors 40 and 41, the space formed by opposing the radiation detectors 40 and 41 is at least 24 cm or less (about 20 cm).
It is possible to dispose a cylindrical structure (for example, corresponding to the head H of the subject P) having a diameter of from about cm to 24 cm. Therefore, the shortest distance between the radiation incident surface of the collimator attached to the detection surface of the radiation detectors 40 and 41 and the surface of this cylindrical structure is 0.5 cm to 2 c.
m.

FIG. 7 is a diagram showing the configuration of two radiation detectors used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention and the positional relationship with the subject. As shown in FIG.
The semiconductor detector arrays 50a and 50b are arranged to face each other across the subject P, and the semiconductor detector arrays 50a and 50b
The thickness t2 of b in the Y direction (perpendicular to the subject P) is constant. Therefore, when a parallel collimator is further installed in SPECT to detect parallel gamma rays, the direction (gamma ray absorption direction) of each semiconductor cell of the semiconductor detector arrays 50a and 50b is the same (Y direction). As in the case of the Anger-type detector, no degradation in the calculated position resolution occurs at each incident position. Therefore, in the peripheral portions of the semiconductor detector arrays 50a and 50b, there is an advantage that the position resolution is improved by the distance to the subject P as compared with the case of the conventional Anger-type detector.

As described above, since the semiconductor detector arrays 50a and 50b have a constant thickness t2 in the Y direction, which is the gamma ray absorption direction, the semiconductor detector arrays 50a and 50b have a greater thickness than the Y direction. The thickness t3 in the absorption direction of the gamma ray incident from the inclined oblique direction is relatively smaller than the thickness t1 of the scintillator of the conventional Anger-type detector. Moreover, the semiconductor detector has a larger absorption coefficient than a scintillator such as NaI. Therefore, even when gamma rays are incident on the semiconductor detector arrays 50a and 50b from a direction oblique to the Y direction, D
The influence of OI is reduced, and the deterioration of the position resolution is reduced.

Thus, in the case of a coincidence-type PET apparatus provided with two concave and curved semiconductor detectors arranged to face each other across the subject P, such a semiconductor detector comes into contact with the subject P. Even if the semiconductor detector moves along the rotation direction D2 around the subject P by shortening the facing distance to such an extent that it does not occur, the influence of the DOI can be relatively reduced. In addition, a 511 keV positron (positron) P by using a concave and curved semiconductor detector is used.
In addition to the increase in the solid angle of coincidence for O, an increase in the solid angle for coincidence by shortening the radius of rotation of the semiconductor detector can be expected.

Also, in the case of a fan beam SPECT having a short focal length for a small organ such as the head, the influence of the DOI can be reduced in the same manner as described above.
Deterioration of position resolution is reduced.

Further, in general, CdTe and cadmium zinc telluride (CZT) semiconductors have a larger absorption coefficient than that of a scintillator such as NaI, so that the thickness of the semiconductor detector can be further reduced. Yes, DOI
Can be further reduced.

FIG. 8 is a diagram showing the configuration of an integrally molded curved three-surface tightness detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention. A curved three-sided compactness detector module as shown in FIG.
1, a semiconductor unit 53 formed on the surface of the substrate 51 and formed of a semiconductor for detecting radiation such as gamma rays;
A plurality of application-specific integrated circuits (A) to be described later formed on the opposite surface (back surface) of the substrate 51
SIC) 52a, 52b, 52c, 52d, and a mounting portion 54 provided on one side surface of the semiconductor portion 53 for mounting the detector module shown in FIG. 8 to a fixing member (not shown) to constitute a radiation detector. Have.

The semiconductor section 53 is divided into a plurality of detection elements (semiconductor cells) 55a,..., 55n and arranged in a matrix, and each of the semiconductor cells 55a,.
5n corresponds to each pixel when reconstructing an image, for example.

Here, the three-surface compactness means a surface adjacent to the three side surfaces (radiation incident surface (detection surface)) of one detector module with almost no dead space (dead zone). This means that the side surface of the other detector module can be joined to the surface on which the section is not provided), which means that a radiation detector having a large field of view can be configured. Note that the dead space referred to here generally corresponds to a space smaller than the size of a semiconductor cell corresponding to one pixel when the radiation detector is viewed from the radiation incident surface side, and is smaller than the size of the semiconductor cell. Spatial resolution and detection sensitivity can be improved by making the size as small as possible. Therefore, even when a plurality of three-sided close-packed detector modules are joined to form a radiation detector, the semiconductor cells are arranged at substantially equal intervals regardless of the presence of a joint between the detector modules. Therefore, a constant spatial resolution can be easily obtained.

It is to be noted that a curved detector module as shown in FIG. 8 can be formed by using a scintillator instead of a semiconductor and arranging a plurality of photodiodes in parallel adjacent to the scintillator, for example.

FIG. 9 is a view showing a radiation detector constituted by an integrally molded curved three-surface close-packed detector module used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. The radiation detector shown in FIG. 9 is configured to be concave with respect to the subject by combining two detector modules shown in FIG. 8 symmetrically. By arranging a plurality of the detector modules 61 and 62 shown in FIG. 9 in the depth direction (arrangement direction) with respect to the drawing, as shown in FIGS.
, 61n, 62a,..., 62n can constitute a large-field two-dimensional radiation detector.

The detector modules 61 and 62 include a plurality of semiconductor cells 63a,.
63n, 64a,... 64n are integrally formed of resin 80 or the like. The detector modules 61 and 62
Include semiconductor cells 63a by detecting gamma rays,
, 63n, 64a,..., 64n, and a signal wiring pattern for supplying an electric detection signal to the subsequent signal processing circuit 69, and semiconductor cells 63a,.
.. 64n are formed with a high-voltage wiring pattern for applying a high voltage.

The semiconductor cells 63a,..., 63n, 64
a,..., 65 used as a gamma ray detection circuit including a preamplifier and a readout circuit for detecting and processing a detection signal from 64n.
n is the semiconductor cell 63a,..., 63n, 64a,.
.. Are arranged on the back side (opposite to the subject side) of the detector modules 61 and 62 so as not to protrude from the formation surface (detection surface) of 64n.

The detector modules 61 and 62 have projections 66a and 66 formed on a copper plate 66 for covering the whole.
It is fixed by screws or the like via b, 66c, 66d. The copper plate 66 has a motherboard 67 mounted thereon.
Electrically separated from the signal processing circuit 69 (blocking digital signal noise) and the ASIC 65a,
.., 65n is configured as a ground plane (ground plane) as large as possible to dissipate the heat generated from 65n.

When the ASICs 65a,..., 65n generate a large amount of heat, the protrusions 66a, 66b, 66c,.
It is possible to adopt an external heat dissipation structure by disposing a forced cooling system (for example, a peltier cooler, a heat pump, a fan) not shown in order to dissipate the heat transmitted to the copper plate 66 through 66d to the outside.

The electrical connection between the ASICs 65a,..., 65n and the signal processing circuit 69 on the motherboard 67 is made via a connector section 68. The signal processing circuit 69 is AS
The output signals of the ICs 65a,..., 65n are signal-processed. The output of the signal processing circuit 69 is the image reconstruction unit 90
, And based on the output, an image reconstruction unit 9
0 reconstructs the RI image. Reconstructed RI
The image is displayed on the display unit 91.

As described above, it is possible to provide a structure which serves both as a mechanical assembly of a detector module having semiconductor cells and as an electrical wiring.

FIG. 12 is a diagram showing an example of the internal structure of a three-sided close-packed detector module constituting a radiation detector used in a nuclear medicine diagnostic apparatus according to the embodiment of the present invention. As shown in FIG. 12, a plurality of semiconductor cells 63 each separated by a thin wall (composed of resin 80)
e, 63f, 63g, 63f and semiconductor cells 63e, 6
A wiring pattern 70 of a voltage application electrode, which is a common wiring for applying a high voltage to 3f, 63g, 63f, and a wiring pattern 71a of a signal extraction electrode for extracting detection signals from the semiconductor cells 63e, 63f, 63g, 63f. ,
71b, 71c and 71d are provided, and these are resin 8
It is integrally formed using 0 or the like. In this case, the voltage application electrode and the signal extraction electrode are respectively arranged in directions parallel to the gamma ray incident direction. Each semiconductor cell is arranged so that the position of the incident surface in the gamma ray incident direction is shifted for each semiconductor cell so as to match the curved surface (detection surface).

Considering that a parallel collimator is provided on the gamma ray incident surface 76, it is desirable to make the gamma ray incident surface 76 a smooth curved surface. Further, in consideration of reducing the thickness of the integrally formed detector module to the extent that the required mechanical strength can be ensured, the detector modules 61a and 62a have a thickness of 1.5 mm to 2.0 mm.
It is designed to be within the range of about mm.

The back surface 7 opposite to the gamma ray incidence surface 76
The back surface 75 is designed not to be a curved surface but to be constituted by a plurality of planes in consideration of the fact that an ASIC 65b or the like is mounted on the 5 and various signal patterns are routed.

FIG. 13 is a view showing another example of the internal structure of the three-sided close-packed detector module constituting the radiation detector used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. The internal structure of the detector module shown in FIG. 13 is basically the same as the internal structure shown in FIG. 12, but the arrangement of each semiconductor cell is different. That is, the position of the incident surface in the gamma ray incident direction is shifted for each pair of two semiconductor cells so that the semiconductor cell fits the curved surface (detection surface). Therefore, two pairs adjacent to each other
In one semiconductor cell, the position of the incident surface in the incident direction of the gamma ray coincides. In this case, the number of sets of semiconductor cells is not limited to two, and the position of the incident surface in the gamma ray incident direction can be shifted for every three or more sets of semiconductor cells.

FIG. 14 shows the internal structure of the connecting portion when a concave radiation detector is formed by combining two three-sided compact detector modules used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. It is a figure showing an example. FIG.
As shown in FIG. 4, each of the detector modules 61 and 62 sandwiches the voltage application electrode 83 between semiconductor cells 81 and 82 which are gamma ray detection elements.
1, 82 are voltage application electrodes 83 and signal extraction electrodes 84,
The structure sandwiched by the layers 85 is formed continuously. An insulator 87 made of resin or the like is provided between the adjacent signal extraction electrodes 85 and 86.

In the detector modules 61 and 62 as shown in FIG. 14, the gap width of the semiconductor cell at the connection portion is different from that of the other portions. However, in the detector module 61, the distance between the centers of the semiconductor cells 81 and 82 adjacent to each other across the voltage application electrode 83 is set to be an integral multiple of the gap width of the adjacent semiconductor cells 81 and 82. 88, 8
9 is set so as to be an integral multiple of the gap width of the semiconductor cells 81 and 82, and the radiation detector is repeatedly moved by a predetermined distance in a predetermined direction by a moving mechanism (not shown), thereby realizing the actual spatial resolution. And the image distortion caused by the mismatch between the resolutions in the image processing and the image processing can be eliminated, and an image having a certain resolution can be obtained.

FIG. 15 shows the internal structure of the connecting portion when a concave radiation detector is formed by combining two three-sided compact detector modules used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. It is a figure showing other examples. In the detector modules 61 and 62 as shown in FIG. 15, the thickness of the insulators 92 and 93 provided near the joint surface 95 of each detector module is determined by the signal extraction electrodes 85 and 86.
By setting the thickness of the insulator 87 provided between them to about の, the semiconductor cells 81 and 82 adjacent to each other with the voltage application electrode 83 interposed therebetween are arranged at equal intervals, so that a constant resolution can be obtained. Becomes possible.

FIG. 16 shows another concave radiation detector having a large field of view constituted by an integrally molded curved three-surface close-packed detector module used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. It is a figure showing an example. The radiation detector shown in FIG. 16 is configured by combining two curved three-sided close-packed detector modules left and right to form a concave shape with respect to the subject, and further includes a plurality of detector modules in the depth direction with respect to the drawing. 101a,..., 101n, 102a,.
., 102n are arranged to form a large field of view. In addition,
In the radiation detector shown in FIG. 10, the two left and right detector modules for forming a concave shape with respect to the subject have the same size, but as with the radiation detector shown in FIG. Left and right 2 to form a concave shape
The two detection modules can be formed in different sizes, and even with such a configuration, the detection surface of the radiation detector can be brought close to the subject.

FIG. 17 is a diagram showing a configuration of a curved two-sided compactness detector module used in a nuclear medicine diagnostic apparatus or the like according to the embodiment of the present invention. A curved two-sided compactness detector module as shown in FIG.
A semiconductor portion 105 formed on the surface of the substrate 103 and configured by a semiconductor for detecting radiation such as gamma rays, and a plurality of A formed on the opposite surface (back surface) of the substrate 103
SICs 104a, 104b, 104c, 104d and mounting portions 106 provided on two opposing side surfaces of the semiconductor portion 105 for mounting the two-surface close-packed detector module to a fixed member (not shown) to constitute a radiation detector. , 107.

The semiconductor section 105 is divided into a plurality of detecting elements (semiconductor cells) 108a,..., 108n and arranged in a matrix, and each of the semiconductor cells 108a,.
.., 108n correspond to each pixel when reconstructing an image, for example.

Here, the two-surface compactness means a surface adjacent to two side surfaces (a radiation incident surface (detection surface)) of one detector module with almost no dead space (dead zone). This means that the side surface of the other detector module can be joined to the surface on which the section is not provided), which means that a radiation detector having a large field of view can be configured. Note that, as described above, the dead space here corresponds to a space smaller than the size of a semiconductor cell that normally corresponds to one pixel when the radiation detector is viewed from the radiation incident surface side. Spatial resolution and detection sensitivity can be improved by making the cell size as small as possible. Therefore, even when a plurality of two-sided compact detector modules are joined to form a radiation detector, the semiconductor cells are arranged at substantially equal intervals regardless of the presence of the joint between the detector modules. Therefore, a constant spatial resolution can be easily obtained.

Also in this case, by using a scintillator instead of a semiconductor and arranging a plurality of photodiodes in parallel adjacent to the scintillator, for example,
A curved detector module as shown in FIG. 17 can also be configured.

The two-sided compactness detector module is configured to be concave with respect to the subject without combining the three-sided compactness detector module shown in FIG.

FIG. 18 is a diagram showing a large-field concave radiation detector constituted by a curved two-surface close-packed detector module used in a nuclear medicine diagnostic apparatus or the like according to the embodiment of the present invention. As described above, since the two-sided compactness detector module shown in FIG. 17 is already formed in a concave shape with respect to the subject, a plurality of such detector modules are arranged in the depth direction (array direction) with respect to the drawing. . Thereby, the plurality of detector modules 109a,.
A large field of view two-dimensional radiation detector provided with n.

FIG. 19 shows another example of the external configuration of a concave radiation detector having a large field of view constituted by a curved dense detector module used in a nuclear medicine diagnostic apparatus according to the embodiment of the present invention. FIG. 20 is a diagram showing a cross section of one detector module constituting the concave radiation detector having a large field of view shown in FIG.

As shown in FIG. 19, detector modules 110a, 110 constituting a concave radiation detector having a large field of view.
, 110n are a plurality of semiconductor cells for detecting gamma rays (112a, 112a,
The semiconductor unit (shown by 112b, 112c, and 112d) (in the detector module 110a, 11
2), and mounting portions 111a, 111b provided adjacent to one side surface of the semiconductor portion.
, 111n, and connectors 113a, 113b,... 113n that are provided on the upper surface of the semiconductor unit, are electrically connected to an ASIC (not shown), and transmit detection signals detected by the respective semiconductor cells to the ASIC. And is molded of resin or the like.

The radiation detector shown in FIG. 19 basically includes the three-sided compactness detector module shown in FIG. 8 or the two-sided compactness detector module shown in FIG. 17 as shown in FIG. 10 or FIG. It is configured by arranging a plurality in the predetermined arrangement direction. However, the detector module 11
0a, 110b,..., 110n correspond to FIG.
The shape and the internal structure are different from those of the detector module shown in FIG.

That is, with respect to the shape, each detector module having a substantially rectangular parallelepiped shape is provided with a protruding portion and a step portion on its upper part. This protruding part
It protrudes along the arrangement direction of the detector modules for forming a large field of view. Therefore, for example, the protruding part 121 of the adjacent detector module 110a is placed on the step part 120 on the upper part of the detector module 110b and combined. Thereby, as compared with the case where a plurality of detector modules are arranged in a predetermined arrangement direction as shown in FIG. 10 or FIG. Can be increased, and a more robust radiation detector can be obtained.

On the other hand, as for the internal structure, as shown in FIG. 20, for example, the detector module 110a includes electrodes (voltage application electrodes and signal extraction electrodes) 114a, 1a attached to the semiconductor cells 112a in the semiconductor section 112.
, 114n and electrodes 114a, 114
b,..., 1114n are formed with a wiring pattern for electrical connection, and have a flexible substrate 115 for transmitting a detection signal detected by the semiconductor cell 112a to the connector 113a. Therefore, by using the flexible substrate on which the wiring pattern is formed, the electrodes 114a, 11a attached to the semiconductor cell 112a can be used.
4b,..., 1114n and an external ASIC provided via the connector 113a can be easily connected.

It is to be noted that, without providing a connector, a signal extracting portion is provided on the flexible substrate to electrically connect directly to the ASIC, or the ASIC is provided on the flexible substrate.
Can be surface-mounted, and such a configuration can simplify the internal structure of the detector module.

With the above configuration, a concave and curved radiation detector, which is difficult to realize with a monolithic type, can be formed relatively easily.

Note that the parallel collimator and the fan beam collimator in the embodiment of the present invention may be configured such that the thickness changes in each part.

[0138]

As described above, according to the present invention, a radiation detector having a detection surface that is concave and curved with respect to the subject is arranged to approach the subject. Therefore, the following advantages are obtained as compared with the conventional Anger-type detector.

(1) The position resolution at the periphery of the radiation detector in SPECT can be remarkably improved.

(2) By installing a fan beam collimator having a fixed focus on the radiation detector, sensitivity and positional resolution can be greatly improved.

(3) The solid angle of the coincidence counting of the positron in the coincidence counting PET can be greatly increased.

(4) SPECT and coincidence-type PE
At the time of detecting a gamma ray at T, the influence of DOI can be extremely reduced.

(5) The radius of gyration of the radiation detector can be reduced as compared with the case of a curved surface detector using a scintillator, so that the coincidence solid angle of coincidence-type PET can be increased.

(6) When a parallel collimator is installed in a radiation detector, it becomes possible to arrange semiconductor cells at equal intervals in the direction of incidence of gamma rays. Can be.

(7) Since a semiconductor detector having a structure in which the ratio of a dead zone electrode portion to a dead zone semiconductor cell portion is small can be used, it is possible to detect gamma rays with high sensitivity.

(8) The thickness of the semiconductor cell in the gamma ray absorption direction can be easily changed, and the sensitivity, the energy resolution, and the time resolution of PET detection can be almost eliminated.

(9) Despite the fact that the radiation detector has a concave curved surface structure, gamma ray detection circuits such as preamplifiers and read-out circuits do not protrude from the detection surface of the semiconductor detector array, and the semiconductor detector array Can be formed on the surface on the side opposite to the detection surface on the gamma ray incident side (object side).

(10) The radiation detector can be miniaturized by employing a structure that combines the mechanical assembly and the electrical wiring of the detector module provided with the semiconductor cells, and also allows the radiation detector to be compact. The number of assembly steps can be greatly reduced.

(11) The radiation detector can be formed by integral molding, and assembling accuracy of the radiation detector can be improved.

(12) Electrical separation and heat dissipation of the radiation detector with respect to the signal processing circuit at the subsequent stage can be efficiently performed.

[Brief description of the drawings]

FIG. 1 is a diagram for explaining a configuration of a conventional Anger-type flat panel detector and a positional relationship with a subject.

FIG. 2 is a diagram illustrating a configuration of a conventional Anger-type curved surface detector and a positional relationship with a subject.

FIG. 3 is a diagram for explaining a configuration of a radiation detector used in a nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention and a positional relationship with a subject.

FIG. 4 is a diagram for explaining another configuration of the radiation detector used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention and a positional relationship with a subject.

FIG. 5 is a diagram for explaining another configuration of the radiation detector used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention and a positional relationship with the subject.

FIG. 6 is a diagram illustrating a case where a fan beam collimator is installed in two radiation detectors used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention and a positional relationship with a subject.

FIG. 7 is a diagram showing a configuration of two radiation detectors used in a nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention and a positional relationship with a subject.

FIG. 8 is a diagram showing a configuration of an integrally molded curved three-sided compactness detector module used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention.

FIG. 9 is a diagram showing a radiation detector constituted by an integrally molded curved three-surface close-packed detector module used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention.

FIG. 10 is a diagram showing a large-field concave radiation detector constituted by an integrally molded curved three-surface close-packed detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention. .

FIG. 11 is a plan view showing a large-field concave radiation detector constituted by an integrally molded curved three-surface close-packed detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention; is there.

FIG. 12 is a diagram illustrating an example of an internal structure of a curved three-surface close-packed detector module constituting a radiation detector used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention;

FIG. 13 is a diagram showing another example of an internal structure of a curved three-surface close-packed detector module constituting a radiation detector used in the nuclear medicine diagnostic apparatus and the like according to the embodiment of the present invention.

FIG. 14 shows an example of an internal structure of a connection portion when a concave radiation detector is configured by combining two three-sided compactness detector modules used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention. FIG.

FIG. 15 shows another example of the internal structure of the connection portion when a concave radiation detector is configured by combining two three-sided compactness detector modules used in the nuclear medicine diagnostic apparatus according to the embodiment of the present invention. It is a figure showing an example.

FIG. 16 shows another example of a large-field concave radiation detector constituted by an integrally molded curved three-surface close-packed detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention. FIG.

FIG. 17 is a diagram showing a configuration of a curved two-sided compactness detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention.

FIG. 18 is a diagram showing a large-field concave radiation detector constituted by a curved two-surface close-packed detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention.

FIG. 19 shows a part of an external configuration of another example of a large-field concave radiation detector constituted by a curved compact detector module used in a nuclear medicine diagnostic apparatus or the like according to an embodiment of the present invention. FIG.

20 is a diagram showing a cross section of one detector module constituting the large-field concave radiation detector shown in FIG. 19;

[Explanation of symbols]

H Head P Subject 30, 30a, 30b, 35, 50a, 50b Semiconductor detector array 31, 32a, 32b, 36 Parallel collimator 32a, 32b Fan beam collimator 37, 40, 41 Radiation detector 51 Substrate 52, 65a, 65b, 65n ASIC 53, 112 Semiconductor part 54, 111a, 111b, 111n Mounting part 55a, 55n, 63a, 63n, 64a, 64n, 8
1, 82, 88, 89, 112a, 112b, 112
c, 112n Semiconductor cells 61, 61a, 61n, 62, 62a, 62n, 110
a, 110b, 110n Detector module 66 Copper plate 66a, 66b, 66c, 66d Projection 67 Motherboard 68 Connector 69 Signal processing circuit 70, 71a, 71b, 71c, 71d Wiring pattern 80 Resin 83 Voltage application electrode 84, 85, 86 Signal extraction electrode 87, 92, 93 Insulator 90 Image reconstruction unit 91 Display unit 113a, 113b, 113n Connector 114a, 114b, 114c, 114n Electrode 115 Flexible board

Claims (66)

[Claims] 1. A plurality of semiconductor cells arranged in a concave shape with respect to a subject and in parallel with each other for detecting radiation from the subject, and a voltage application for applying a voltage to the semiconductor cells. A radiation detector comprising: an electrode; 2. The semiconductor device according to claim 1, wherein the plurality of semiconductor cells have a concave shape along the surface of the subject by arranging the positions of the incident surfaces in the incident direction of the radiation continuously shifted. The radiation detector according to claim 1. 3. In the plurality of semiconductor cells, the position of the incident surface in the incident direction of the radiation is continuously shifted for each set of two or more semiconductor cells,
The radiation detector according to claim 1, wherein the radiation detector has a concave shape along the surface of the subject. 4. The radiation detector according to claim 1, wherein the plurality of semiconductor cells are arranged in a matrix. 5. The radiation detector according to claim 1, wherein the thickness of the plurality of semiconductor cells in the absorption direction of the incident radiation is all constant. 6. The radiation detector according to claim 1, wherein a thickness of the radiation detector in a radiation absorption direction is different between a central part of the radiation detector and a peripheral part thereof. 7. The radiation detector according to claim 6, wherein a thickness of the radiation detector in a radiation absorption direction is larger at a peripheral portion than at a central portion of the radiation detector. 8. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. A radiation detector, comprising: a semiconductor detector array having a detection surface formed in a concave shape; and a parallel collimator provided along a detection surface of the semiconductor detector array. 9. A detection signal from each semiconductor cell is formed on the back side of the semiconductor detection array opposite to the detection surface so as not to protrude from the range of the size of the detection surface. The radiation detector according to claim 8, further comprising a processing circuit, wherein the processing circuit is formed integrally with the semiconductor detector array. 10. A semiconductor device comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. A radiation detector, comprising: two semiconductor detector arrays each having a detection surface formed in a concave shape, wherein the two semiconductor detector arrays are opposed to each other with the subject interposed therebetween. 11. A semiconductor device comprising: a plurality of semiconductor cells, each of which is arranged in parallel, for detecting radiation from a subject, and a voltage application electrode for applying a voltage to the semiconductor cells; A radiation detector, comprising: two semiconductor detector arrays each having a detection surface formed in a concave shape, wherein the two semiconductor detector arrays are installed at an arbitrary angle across the subject. 12. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. A radiation detector, comprising: three or more semiconductor detector arrays each having a detection surface formed in a concave shape, wherein the three or more semiconductor detector arrays are provided with the subject interposed therebetween. 13. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. A radiation detector, comprising: a plurality of semiconductor detector arrays having a detection surface formed in a concave shape, wherein the plurality of semiconductor detector arrays are arranged one-dimensionally or two-dimensionally. 14. The semiconductor detector array is formed such that the thickness of a portion other than the semiconductor cell portion in a predetermined direction of the detection surface is approximately 1/10 or less of the thickness of the semiconductor cell portion. The radiation detector according to any one of claims 8 to 13, wherein: 15. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. The semiconductor device includes at least one semiconductor detector array having a detection surface formed in a concave shape, and at least one fan beam collimator provided along the detection surface of the semiconductor detector array and having a constant focal point. A radiation detector. 16. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. Two semiconductor detector arrays, each having a detection surface formed in a concave shape and opposed to each other, and a fan beam collimator provided along the detection surface of each of the two semiconductor detector arrays and having a different focal position. A radiation detector, comprising: 17. A semiconductor device comprising: a plurality of semiconductor cells, each arranged in parallel, for detecting radiation from a subject, and a voltage application electrode for applying a voltage to the semiconductor cells; On the other hand, two semiconductor detector arrays whose detection surfaces are formed in a concave shape and are installed at an arbitrary angle, and fan beams respectively provided along the detection surfaces of the two semiconductor detector arrays and each having a constant focal point A radiation detector, comprising: a collimator. 18. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. In contrast, two semiconductor detector arrays each having a detection surface formed in a concave shape and installed at an arbitrary angle, and a fan beam collimator provided along the detection surfaces of the two semiconductor detector arrays and having different focal positions A radiation detector comprising: 19. A semiconductor device comprising: a plurality of semiconductor cells, each arranged in parallel, for detecting radiation from a subject, and a voltage application electrode for applying a voltage to the semiconductor cells; On the other hand, two semiconductor detector arrays whose detection surfaces are formed in a concave shape and are installed at arbitrary positions, and fan beams respectively provided along the detection surfaces of the two semiconductor detector arrays and each having a fixed focal point A radiation detector, comprising: a collimator. 20. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. On the other hand, two semiconductor detector arrays each having a detection surface formed in a concave shape and installed at an arbitrary position, and a fan beam collimator provided along the detection surface of the semiconductor detector array and having different focal positions. A radiation detector, comprising: 21. A semiconductor device, comprising: a plurality of semiconductor cells each arranged in parallel, for detecting radiation from a subject; and a voltage application electrode for applying a voltage to the semiconductor cells. Three or more semiconductor detector arrays each having a detection surface formed in a concave shape, and fan beams respectively provided along the detection surfaces of the three or more semiconductor detector arrays and having different focal positions A radiation detector, comprising: a collimator. 22. Two radiation detector arrays each having a plurality of detection elements arranged in a concave shape with respect to the subject and in parallel with each other, and each of which has a plurality of detection elements for detecting radiation from the subject. A radiation detector, wherein the detector array is arranged to face each other across the subject so that each detection surface is formed along the surface of the subject. 23. The apparatus according to claim 23, further comprising collimators attached to the detection surfaces of the two radiation detector arrays, respectively.
The two radiation detector arrays each have a concave detection surface in which a cylindrical structure having a diameter of 24 cm or less can be arranged in a space formed by the opposed arrangement, and the radiation incident surface of the collimator and the cylindrical 23. The radiation detector according to claim 22, wherein the shortest distance from the surface of the structure is in the range of 0.5 cm to 2 cm. 24. The radiation detector array according to claim 23, wherein each end of the radiation detector array is closely arranged.
3. A radiation detector according to claim 1. 25. A radiation detector comprising a plurality of detection elements arranged in a concave shape with respect to a subject and in parallel with each other, and for detecting radiation from the subject. 26. Two curved detector modules each having a plurality of detection elements for detecting radiation arranged in parallel, wherein the two detector modules are combined to form a concave shape with respect to the subject. A radiation detector characterized in that: 27. The radiation detector according to claim 25, wherein the plurality of detection elements are formed of a semiconductor or a scintillator. 28. The radiation detector according to claim 25, wherein the plurality of detection elements are arranged so that the positions of the incident surfaces in the incident direction of the radiation are shifted. 29. The apparatus according to claim 25, further comprising: a detector module on which the plurality of detection elements are arranged, wherein both ends of the detector module are provided with portions that do not contribute to radiation detection. 3. A radiation detector according to claim 1. 30. The two detector modules, each having one end connected and combined, and the other end provided with a portion that does not contribute to radiation detection. Item 27. The radiation detector according to Item 26. 31. The radiation detector according to claim 25, wherein the plurality of detection elements are arranged in a matrix. 32. A plurality of detector modules each having a plurality of detection elements arranged in a concave shape with respect to the subject and in parallel with each other, and each of which has a plurality of detection elements for detecting radiation from the subject. A radiation detector, wherein the detector modules are arranged in a predetermined direction, have a step portion and a projecting portion, and the projecting portion is mounted on a step portion of an adjacent detector module and is combined. 33. Each of the detector modules has a flexible substrate electrically connected to the plurality of detection elements, and the flexible substrate processes a detection signal detected by each of the detection elements. 33. The radiation detector according to claim 32, wherein a processing circuit is connectable. 34. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector is arranged in a concave shape with respect to the subject and each is arranged in parallel with the subject. A nuclear medicine diagnostic apparatus comprising: a plurality of semiconductor cells; and a voltage application electrode for applying a voltage to the semiconductor cells. 35. The semiconductor device according to claim 35, wherein the plurality of semiconductor cells form a concave shape along the surface of the subject by arranging the positions of the incident surfaces in the incident direction of the radiation continuously shifted. A nuclear medicine diagnostic apparatus according to claim 34. 36. In the plurality of semiconductor cells, the position of the incident surface in the incident direction of the radiation is continuously shifted for each set of two or more semiconductor cells, so that the position along the surface of the subject is increased. 35. The nuclear medicine diagnostic apparatus according to claim 34, wherein the apparatus has a concave shape. 37. The nuclear medicine diagnostic apparatus according to claim 34, wherein the plurality of semiconductor cells are arranged in a matrix. 38. The nuclear medicine diagnostic apparatus according to claim 34, wherein the thickness of the plurality of semiconductor cells in the absorption direction of the incident radiation is all constant. 39. The nuclear medicine diagnostic apparatus according to claim 34, wherein a thickness of the radiation detector in a radiation absorption direction is different between a central portion and a peripheral portion of the radiation detector. 40. The nuclear medicine diagnostic apparatus according to claim 39, wherein the thickness of the radiation detector in the direction of absorption is thicker at the periphery than at the center of the radiation detector. 41. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; A semiconductor detector array having a voltage application electrode for applying a voltage, and a detection surface formed in a concave shape with respect to the subject; and a parallel provided along the detection surface of the semiconductor detector array. A nuclear medicine diagnostic apparatus comprising a collimator. 42. A detection signal from each semiconductor cell is formed on the back side of the semiconductor detection array opposite to the detection surface so as not to protrude from the range of the size of the detection surface. 42. The nuclear medicine diagnostic apparatus according to claim 41, further comprising a processing circuit, wherein the processing circuit is formed integrally with the semiconductor detector array. 43. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; A voltage application electrode for applying a voltage; and two semiconductor detector arrays each having a detection surface formed in a concave shape with respect to the subject. A nuclear medicine diagnostic apparatus characterized in that the nuclear medicine diagnostic apparatus is placed opposite to and sandwiched therebetween. 44. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; A voltage application electrode for applying a voltage; and two semiconductor detector arrays each having a detection surface formed in a concave shape with respect to the subject. A nuclear medicine diagnostic apparatus characterized by being installed at an arbitrary angle between the two. 45. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; A voltage application electrode for applying a voltage, comprising three or more semiconductor detector arrays, the detection surface of which is formed in a concave shape with respect to the subject, and the three or more semiconductor detector arrays A nuclear medicine diagnostic apparatus, which is installed with the subject interposed therebetween. 46. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; A plurality of semiconductor detector arrays each having a voltage application electrode for applying a voltage and having a detection surface formed in a concave shape with respect to the subject, wherein the plurality of semiconductor detector arrays are one-dimensional or two-dimensional. A nuclear medicine diagnostic device characterized by being arranged in three dimensions. 47. The semiconductor detector array is formed such that the thickness of a portion other than the semiconductor cell portion in a predetermined direction of the detection surface is approximately 1/10 or less of the thickness of the semiconductor cell portion. The nuclear medicine diagnostic apparatus according to any one of claims 41 to 46, wherein: 48. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; One or more semiconductor detector arrays having a voltage application electrode for applying a voltage, and a detection surface formed in a concave shape with respect to the subject, and along a detection surface of the semiconductor detector array A nuclear medicine diagnostic apparatus, comprising: at least one fan beam collimator having a fixed focal point. 49. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Two semiconductor detector arrays each having a voltage application electrode for applying a voltage, having a detection surface formed in a concave shape with respect to the subject, and opposed to each other, and detecting the two semiconductor detector arrays A nuclear medicine diagnostic apparatus comprising: a fan beam collimator provided along a surface and having a different focal position. 50. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Two semiconductor detector arrays each having a voltage application electrode for applying a voltage, having a detection surface formed in a concave shape with respect to the subject, and being installed at an arbitrary angle; and the two semiconductor detector arrays. And a fan beam collimator provided along the detection surface and having a constant focal point. 51. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Two semiconductor detector arrays each having a voltage application electrode for applying a voltage, having a detection surface formed in a concave shape with respect to the subject, and being installed at an arbitrary angle; and the two semiconductor detector arrays. And a fan beam collimator provided along the detection surface and having a different focal position. 52. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Two semiconductor detector arrays each having a voltage application electrode for applying a voltage, having a detection surface formed in a concave shape with respect to the subject, and being installed at an arbitrary position; and the two semiconductor detector arrays. And a fan beam collimator provided along the detection surface and having a constant focal point. 53. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Two semiconductor detector arrays each having a voltage application electrode for applying a voltage, having a detection surface formed in a concave shape with respect to the subject, and being installed at an arbitrary position; and the two semiconductor detector arrays. And a fan beam collimator provided along the detection surface and having a different focal position. 54. A nuclear medicine diagnostic apparatus comprising a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises: a plurality of semiconductor cells each arranged in parallel; Three or more semiconductor detector arrays each having a voltage application electrode for applying a voltage and having a detection surface formed in a concave shape with respect to the subject and arranged; and the three or more semiconductor detectors A nuclear medicine diagnostic apparatus comprising: a fan beam collimator provided along a detection surface of an array and having a different focal position. 55. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector is arranged in a concave shape with respect to the subject and each is arranged in parallel with the subject. The radiation detector array includes two radiation detector arrays each having a plurality of detection elements, and the two radiation detector arrays are opposed to each other across the subject so that each detection surface is formed along the surface of the subject. A nuclear medicine diagnostic device characterized by being performed. 56. The apparatus according to claim 56, further comprising collimators attached to the detection surfaces of the two radiation detector arrays, respectively.
The two radiation detector arrays each have a concave detection surface in which a cylindrical structure having a diameter of 24 cm or less can be arranged in a space formed by the opposed arrangement, and the radiation incident surface of the collimator and the cylindrical The nuclear medicine diagnostic apparatus according to claim 55, wherein a shortest distance between the surface of the structure and the surface is within a range of 0.5 cm to 2 cm. 57. The radiation detector array according to claim 55, wherein each end is closely arranged.
A nuclear medicine diagnostic apparatus according to claim 1. 58. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector comprises a plurality of radiation detectors arranged in a concave shape with respect to the subject and in parallel with each other. A nuclear medicine diagnostic apparatus, comprising: 59. A nuclear medicine diagnostic apparatus provided with a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector has two curved surfaces each having a plurality of detection elements arranged in parallel. A nuclear medicine diagnostic apparatus, comprising: a detector module; and combining the two detector modules to form a concave shape with respect to the subject. 60. The nuclear medicine diagnostic apparatus according to claim 58, wherein the plurality of detection elements are formed of a semiconductor or a scintillator. 61. The nuclear medicine diagnostic apparatus according to claim 58, wherein the plurality of detection elements are arranged so that the positions of the incident surfaces in the incident direction of the radiation are shifted. 62. A detector module having a plurality of detection elements arranged thereon, wherein both ends of the detector module are provided with portions that do not contribute to radiation detection. A nuclear medicine diagnostic apparatus according to claim 1. 63. The two detector modules are connected to each other at one end, and each of the other ends is provided with a portion that does not contribute to the detection of radiation. 61. A nuclear medicine diagnostic apparatus according to item 59. 64. The nuclear medicine diagnostic apparatus according to claim 58, wherein the plurality of detection elements are arranged in a matrix. 65. A nuclear medicine diagnostic apparatus including a radiation detector for detecting radiation emitted from a subject, wherein the radiation detector is arranged in a concave shape with respect to the subject and in parallel with each other. A plurality of detector modules each having a plurality of detection elements, wherein each of the detector modules is arranged in a predetermined direction, has a step portion and a projecting portion, and the projecting portion has a step portion of an adjacent detector module. A nuclear medicine diagnostic apparatus characterized by being combined with a nuclear medicine. 66. Each of the detector modules has a flexible substrate electrically connected to the plurality of detection elements, and the flexible substrate processes a detection signal detected by each of the detection elements. The nuclear medicine diagnostic apparatus according to claim 65, wherein a processing circuit is connectable.