PET device, PET-MRI apparatus, and image processing method

1. A positron emission computed tomography (PET) device comprising:

a first PET detector having a ring shape and having a first radius, the first PET detector including a plurality of first scintillators arranged in a ring shape and configured to detect a plurality of gamma rays emitted from positron-emitting radionuclides injected into a subject, the ring shape of the plurality of first scintillators defining an outer circumferential side;

a second PET detector having a ring shape and having a second radius greater than the first radius, the second PET detector including a plurality of second scintillators arranged in a ring shape and configured to detect at least one gamma ray of the plurality of gamma rays that has passed through the first scintillators, the ring shape of the plurality of second scintillators defining an inner circumferential side, wherein the first PET detector and the second PET detector are concentric, wherein the outer circumferential side of the first plurality of scintillators faces the inner circumferential side of the second plurality of scintillators, wherein a pixel size of the second scintillators is larger than a pixel size of the first scintillators, wherein a length of the second PET detector in its axial direction is longer than that of the first PET detector; and

a processor in communication with the plurality of first scintillators and the plurality of second scintillators, the processor configured to

acquire first counted information including a detection position, an energy value, and a detection time regarding the plurality of gamma rays detected by one of the first scintillators and acquire second counted information including a detection position, an energy value, and a detection time regarding the at least one gamma ray detected by one of the second scintillators;

when a difference between the detection time comprised by the first counted information and the detection time comprised by the second counted information is within a time window width that is selected to determine whether the first counted information and the second counted information correspond to said at least one gamma ray, generate corrected counted information for said at least one gamma ray by adding the energy value comprised by the second counted information for said at least one gamma ray to the energy value comprised by the first counted information for said at least one gamma ray;

based on the corrected counted information, generate simultaneous counted information based on a combination of the corrected counted information on simultaneous detection of the plurality of gamma rays emitted from the positron-emitting radionuclides; and

reconstruct a PET image in accordance with the simultaneous counted information.

2. The PET device according to claim 1 , wherein the first scintillators have a first thickness, and the second scintillators have a second thickness that is greater than the first thickness.

3. The PET device according to claim 1 , further comprising:

a third PET detector having a ring shape and having a third radius, the third PET detector including a plurality of third scintillators arranged in a ring shape defining an outer circumferential side, arranged apart from the first scintillators along the axial direction of the first scintillators, and configured to detect a plurality of second gamma rays emitted from the positron-emitting radionuclides injected into the subject; and

a fourth PET detector having a ring shape and having a fourth radius greater third radius, the fourth PET detector including a plurality of fourth scintillators arranged in a ring shape and configured to detect at least one second gamma ray of the plurality of second gamma rays that has passed through the third scintillators, the ring shape of the plurality of fourth scintillators defining an inner circumferential side, wherein the third PET detector and the fourth PET detector are concentric, wherein the outer circumferential side of the third plurality of scintillators faces the inner circumferential side of the fourth plurality of scintillators, and wherein the third PET detector and the fourth PET detector are axially spaced from the first PET detector and the second PET detector,

wherein

the processor acquires third counted information including a detection position, an energy value, and a detection time regarding the plurality of second gamma rays detected by one of the third scintillators and acquires fourth counted information including a detection position, an energy value, and a detection time regarding the at least one second gamma ray detected by one of the fourth scintillators and determines the first counted information and the second counted information for said at least one gamma ray, and the third counted information and the fourth counted information for said at least one second gamma ray,

the processor generates said corrected counted information as first corrected counted information for said at least one gamma ray by adding the energy value comprised by the second counted information for said at least one gamma ray to the energy value comprised by the first counted information for said at least one gamma ray and generates second corrected counted information for said at least one second gamma ray by adding the energy value comprised by the fourth counted information for said at least one second gamma ray to the energy value comprised by the third counted information for said at least one second gamma ray, and

based on the first corrected counted information and the second corrected counted information, the processor generates the simultaneous counted information based on a combination of the first corrected counted information on the simultaneous detection of the plurality of gamma rays emitted from the positron-emitting radionuclides, a combination of the second corrected counted information on simultaneous detection of the plurality of second gamma rays emitted from the positron-emitting radionuclides, and a combination of the first corrected counted information and the second corrected counted information on simultaneous detection of the plurality of gamma rays and the plurality of second gamma rays emitted from the positron-emitting radionuclides, each of the combinations comprising a sum of corresponding ones of the energy values.

4. The PET device according to claim 1 , wherein

the processor is configured to compare an energy value comprised by the generated corrected counted information with an energy value of the plurality of gamma rays emitted from the positron-emitting radionuclides and chooses the corrected counted information where a difference between the energy value comprised by the generated counted information and the energy value of the plurality of gamma rays emitted from the positron-emitting radionuclides is within a predetermined range, and

the processor is configured such that, based on the corrected counted information which is chosen, the processor generates the simultaneous counted information.

5. A positron emission computed tomography-magnetic resonance imaging (PET-MRI) apparatus comprising:

a static magnetic field magnet configured to generate a static magnetic field in a cylindrical bore;

a high-frequency coil configured to detect a magnetic resonance signal emitted from a subject placed in the static magnetic field, in response to application of a high-frequency pulse and a gradient magnetic field to the subject;

a first PET detector having a ring shape and having a first radius, the first PET detector including a plurality of first scintillators arranged in a ring shape and configured to detect a plurality of gamma rays that are emitted from positron-emitting radionuclides that are injected into the subject, the ring shape of the plurality of first scintillators defining an outer circumferential side;

a second PET detector having a ring shape and having a second radius greater than the first radius, the second PET detector including a plurality of second scintillators arranged in a ring shape and configured to detect at least one gamma ray of the plurality of gamma rays that has passed through the first scintillators, the ring shape of the plurality of second scintillators defining an inner circumferential side, wherein the first PET detector and the second PET detector are concentric, wherein the outer circumferential side of the first plurality of scintillators faces the inner circumferential side of the second plurality of scintillators, wherein a pixel size of the second scintillators is larger than a pixel size of the first scintillators, wherein a length of the second PET detector in its axial direction is longer than that of the first PET detector; and

a processor in communication with the high-frequency coil, the plurality of first scintillators, and the plurality of second scintillators, the processor configured to

reconstruct an MR image based on the magnetic resonance signal detected by the high-frequency coil;

acquire first counted information including a detection position, an energy value, and a detection time regarding the plurality of gamma rays detected by one of the first scintillators and acquire second counted information including a detection position, an energy value, and a detection time regarding the at least one gamma ray detected by one of the second scintillators;

when a difference between the detection time comprised by the first counted information and the detection time comprised by the second counted information is within a time window width that is selected to determine whether the first counted information and the second counted information correspond to said at least one gamma ray, generate corrected counted information for said at least one gamma ray by adding the energy value comprised by the second counted information for said at least one gamma ray to the energy value comprised by the first counted information for said at least one gamma ray;

based on the corrected counted information, generate simultaneous counted information based on a combination of the corrected counted information on simultaneous detection of the plurality of gamma rays emitted from the positron-emitting radionuclides; and

reconstruct a PET image in accordance with the simultaneous counted information.

6. The PET-MRI apparatus according to claim 5 , wherein the first scintillators have a first thickness, and the second scintillators have a second thickness that is greater than the first thickness.

7. The PET-MRI apparatus according to claim 5 , further comprising:

a third PET detector having a ring shape and having a third radius, the third PET detector including a plurality of third scintillators arranged in a ring shape to define an outer circumferential side and arranged apart from the first scintillators along an axial direction of the cylindrical bore such that a magnetic field center of the static magnetic field is between the first scintillators and the third scintillators; and

a fourth PET detector having a ring shape and having a fourth radius greater than the third radius, the fourth PET detector including a plurality of fourth scintillators arranged in a ring shape and configured to detect at least one second gamma ray of the plurality of second gamma rays that has passed through the third scintillators, the ring shape of the plurality of fourth scintillators defining an inner circumferential side, wherein the third PET detector and the fourth PET detector are concentric, wherein the outer circumferential side of the third plurality of scintillators faces the inner circumferential side of the fourth plurality of scintillators, and wherein the third PET detector and the fourth PET detector are axially spaced from the first PET detector and the second PET detector,

wherein

the processor acquires third counted information including a detection position, an energy value, and a detection time regarding the plurality of second gamma rays detected by one of the third scintillators and acquires fourth counted information including a detection position, an energy value, and a detection time regarding the at least one second gamma ray detected by one of the fourth scintillators and determines the first counted information and the second counted information for a said at least one gamma ray, and the third counted information and the fourth counted information for said at least one second gamma ray,

the processor generates said corrected counted information as first corrected counted information for said at least one gamma ray by adding the energy value comprised by the second counted information for said at least one gamma ray to the energy value comprised by the first counted information for said at least one gamma ray and generates second corrected counted information for said at least one second gamma ray by adding the energy value comprised by the fourth counted information for said at least one second gamma ray to the energy value comprised by the third counted information for said at least one second gamma ray, and

based on the first corrected counted information and the second corrected counted information, the processor generates simultaneous counted information based on a combination of the first corrected counted information on the simultaneous detection of the plurality of gamma rays emitted from the positron-emitting radionuclides, a combination of the second corrected counted information on simultaneous detection of the plurality of second gamma rays emitted from the positron-emitting radionuclides, and a combination of the first corrected counted information and the second corrected counted information on simultaneous detection of the plurality of gamma rays and plurality of second gamma rays emitted from the positron-emitting radionuclides, each of the combinations comprising a sum of corresponding ones of the energy values.

8. The PET-MRI apparatus according to claim 7 , wherein the processor is configured such that the processor further generates the simultaneous counted information to further comprise a combination of the first corrected counted information and the fourth counted information on the simultaneous detection of the plurality of gamma rays and the plurality of second gamma rays and a combination of the third counted information and the second counted information on the simultaneous detection of the plurality of gamma rays and the plurality of second gamma rays.

9. The PET-MRI apparatus according to claim 7 , further comprising:

a driver configured to move the subject along the axial direction of the cylindrical bore; and

wherein the processor is configured to control the driver such that the driver moves a region to be imaged of the subject to an approximate center of any one of the plurality of first scintillators and the plurality of third scintillators and an approximately center position of an area between the first scintillators and the third scintillators, perform control such that the PET image is captured when the region to be imaged is moved to an approximately center position of the first scintillators or the third scintillators, and control the MRI image and/or the PET image to be captured when the region to be imaged is moved to the approximately center position of the area between the first scintillators and the third scintillators.

10. The PET-MRI apparatus according to claim 5 , wherein, upon generation of the simultaneous counted information, when the simultaneous counted information is on one of the plurality of gamma rays that has passed through an effective imaging area for MR images, the processor stores the simultaneous counted information in association with simultaneous imaging identifying information representing that the simultaneous counted information is information on an area where the MR image and the PET image can be captured simultaneously.

11. The PET-MRI apparatus according to claim 5 , wherein the processor is configured such that

the processor compares an energy value comprised by the generated corrected counted information with the energy value of the plurality of gamma rays emitted from the positron-emitting radionuclides and chooses corrected counted information where a difference between the energy value comprised by the generated corrected counted information and the energy value of the plurality of gamma rays emitted from the positron-emitting radionuclides is within a predetermined range, and

based on the corrected counted information, which is chosen by the processor, the processor generates the simultaneous counted information.

12. The PET-MRI apparatus according to claim 5 , wherein each of the first scintillators is formed such that its length in an axial direction of the ring shape is smaller than that of each of the second scintillators.

13. An image processing method comprising:

detecting, by a first PET detector having a ring shape and having a first radius, the first PET detector including a plurality of first scintillators arranged in a ring shape to define an outer circumferential side, a plurality of gamma rays that are emitted from positron-emitting radionuclides that are injected into a subject;

detecting, by a second PET detector having a ring shape and having a second radius greater than the first radius, the second PET detector including a plurality of second scintillators arranged in a ring shape, at least one gamma ray of the plurality of gamma rays that has passed through the first scintillators, the ring shape of the plurality of second scintillators defining an inner circumferential side, wherein the first PET detector and the second PET detector are concentric, wherein the outer circumferential side of the first plurality of scintillators faces the inner circumferential side of the second plurality of scintillators, wherein a pixel size of the second scintillators is larger than a pixel size of the first scintillators, and wherein a length of the second PET detector in its axial direction is longer than that of the first PET detector;

acquiring first counted information including a detection position, an energy value, and a detection time regarding the plurality of gamma rays detected by one of the first scintillators and acquiring second counted information including a detection position, an energy value, and a detection time regarding the at least one gamma ray detected by one of the second scintillators;

when a difference between the detection time comprised by the first counted information and the detection time comprised by the second counted information is within a time window width that is selected to determine whether the first counted information and the second counted information correspond to said at least one gamma ray, generating corrected counted information for said at least one gamma ray by adding the energy value contained in the second counted information for said at least one gamma ray to the energy value contained in the first counted information for said at least one gamma ray;

generating, as simultaneous counted information, a combination of the corrected counted information on simultaneous detection of the plurality of gamma rays emitted from the positron-emitting radionuclides, based on the corrected counted information; and

reconstructing a PET image in accordance with the simultaneous counted information.

14. The PET device according to claim 1 , wherein each of the first scintillators is formed such that its length in an axial direction of the ring shape is smaller than that of each of the second scintillators.