CN105395208A - PET detection device with single photon emission computed tomography function - Google Patents
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- CN105395208A CN105395208A CN201410458364.4A CN201410458364A CN105395208A CN 105395208 A CN105395208 A CN 105395208A CN 201410458364 A CN201410458364 A CN 201410458364A CN 105395208 A CN105395208 A CN 105395208A
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Abstract
The invention provides a PET detection device with a single photon emission computed tomography function. The PET detection device comprises a first panel detector and a second panel detector. At least one of the first panel detector and the second panel detector comprises a detector shell, a flickering detection mechanism arranged in the detector shell and used for detecting emitted gamma photons, and a collimator arranged on the light collection face of the flickering detection mechanism. The collimator is suitable for single photon computed tomography, and can move relative to the light collection face of the flickering detection mechanism so as to face or pass by the light collection face of the flickering detection mechanism. By means of the PET detection device, single photon emission computed tomography can be achieved when the collimator faces the light collection face of the flickering detection mechanism, the positron emission computed tomography function is achieved when the collimator passes by the light collection face of the flickering detection mechanism, the PET detection device is diverse in function, and the use efficiency of the PET detection device is improved.
Description
Technical Field
The utility model relates to a nuclear medicine imaging technology field, concretely relates to PET detection device with single photon emission imaging function.
Background
Nuclear medicine imaging technology is the most typical and straightforward application of nuclear science and nuclear technology in medical diagnostics. The nuclear medicine imaging technology can image truly, can completely and directly display physiological and pathological processes at a cellular level or a molecular level, can carry out early diagnosis at the molecular level on a plurality of diseases such as tumors, cardiovascular diseases, nervous systems and the like, not only represents the development direction of medical imaging, but also has wide market prospect.
The nuclear medicine imaging technology mainly includes a Single-photon emission computed tomography (SPECT) technology and a Positron Emission Tomography (PET) technology. The SPECT technology develops on the basis of a Gamma camera, has all functions of the Gamma camera, and has unique points in the aspects of dynamic function examination or early diagnosis by adding various newly developed radiopharmaceuticals, so that the SPECT technology is increasingly and widely applied clinically. The PET technology is a leading technology in modern nuclide imaging technology, can use human body substance composition elements to manufacture radiopharmaceuticals, is particularly suitable for the research of human body physiology and functions, and is called as a 'biochemical layer' or a 'living body layer' due to clear and real imaging; the PET technology also has unique advantages in the aspect of acquiring the functional information of certain organs or lesions of human bodies or animals, such as high sensitivity and high accuracy, and the used radioactive isotopes are basic elements closely related to life activities, are easy to mark various life activities, have pertinence and the like.
With the rapid development of nuclear medicine imaging technology, the search and development of special nuclear medicine imaging equipment with high-precision diagnosis capability become a hot point of research in recent years. Compared with a whole-body imaging system, the special nuclear medicine imaging equipment has higher detection sensitivity and spatial resolution, and is very beneficial to accurate diagnosis and accurate positioning of local lesions. For example, Naviscan corporation of America introduced a flat panel proprietary PET device with spatial resolution above that of human PET; for example, Dilonechnologices, USA, has introduced a special SPECT device of flat type, and can find early breast cancer lesion of about 1mm, and so on. The above products have only a single mode of imaging function.
Disclosure of Invention
To some or all of the problems in the prior art, the present disclosure provides a PET detection device with a single photon emission imaging function, thereby enabling an imaging function in two modes.
Additional features and advantages of the disclosure will be set forth in the detailed description which follows, or in part will be obvious from the description, or may be learned by practice of the disclosure.
According to one aspect of the disclosure, a PET detection device with single photon emission imaging function comprises a first flat-plate detector and a second flat-plate detector; at least one of the first and second flat panel detectors comprises:
a probe housing;
the scintillation detection mechanism is arranged in the detector shell and used for detecting incident gamma photons;
the collimator is arranged on the light receiving surface of the scintillation detection mechanism;
the collimator is suitable for single photon imaging and can move relative to the light receiving surface of the scintillation detection mechanism so as to face the light receiving surface of the scintillation detection mechanism or stagger the light receiving surface of the scintillation detection mechanism.
In an example embodiment of the present disclosure, the first flat panel detector and the second flat panel detector are identical.
In an example embodiment of the present disclosure, a sliding groove is disposed on the detector housing, and a sliding rail adapted to the sliding groove is correspondingly disposed on the collimator; or, a slide rail is arranged on the detector shell, and a sliding groove matched with the slide rail is correspondingly arranged on the collimator.
In an example embodiment of the present disclosure, further comprising:
the driving mechanism is used for driving the collimator to move relative to the light receiving surface of the flicker detection mechanism;
and the control mechanism is used for triggering the driving mechanism to drive the collimator to move relative to the light receiving surface of the flicker detection mechanism.
In an example embodiment of the present disclosure, the first flat panel detector and the second flat panel detector are parallel to each other or at a preset angle.
In an example embodiment of the present disclosure, the collimator includes: a low energy collimator, a medium energy collimator, or a high energy collimator; or,
the collimator includes: a parallel-hole collimator, a fan collimator, a pinhole collimator, or a rotating plate collimator.
In an example embodiment of the present disclosure, the flicker detection mechanism is formed by splicing a plurality of flicker detection modules; each of the flicker detection modules includes:
a scintillation crystal array for receiving incident gamma photons and emitting scintillation light;
a light guide device having a first end connected to the array of scintillation crystals;
a light detector, the input end of which is connected with the second end of the light guide device; and the number of the first and second groups,
and the position logic circuit is connected with the output end of the light detector.
In an example embodiment of the present disclosure, a scintillation crystal in the array of scintillation crystals comprises: LYSO scintillation crystals, LaBr3 scintillation crystals, YSO scintillation crystals, YAP scintillation crystals, GSO scintillation crystals, or BGO scintillation crystals.
In an example embodiment of the present disclosure, the light guide device is a tapered light guide.
In an example embodiment of the present disclosure, the photodetector includes a photomultiplier tube or a silicon photomultiplier tube.
In the PET detection device with the single photon emission imaging function, the movable collimator is arranged on the light receiving surface of the scintillation detection mechanism of the flat panel detector, so that single photon emission imaging can be realized when the collimator faces the light receiving surface of the scintillation detection mechanism, the positron emission imaging function is realized when the collimator is staggered with the light receiving surface of the scintillation detection mechanism, and the service efficiency of the PET detection device is improved through one machine with multiple purposes.
Drawings
The above and other features and advantages of the present disclosure will become more apparent by describing in detail exemplary embodiments thereof with reference to the attached drawings.
FIG. 1 is a schematic structural diagram of a flat-panel PET detection device in the prior art;
FIG. 2 is a schematic diagram of a flat panel detector of FIG. 1;
FIG. 3 is a schematic structural diagram of a PET detection device with single photon emission imaging in an example embodiment of the disclosure;
FIG. 4 is a schematic diagram of a flat panel detector of FIG. 3;
FIG. 5 is a schematic diagram of a scintillation detection mechanism in an example embodiment of the present disclosure;
FIG. 6 is a schematic diagram of a scintillation detection module of FIG. 5;
fig. 7 and 8 are schematic diagrams of fig. 3 showing different combination angles of a PET detection device with single photon emission imaging function according to an example embodiment of the disclosure.
Description of reference numerals:
10: line of response
11: first flat panel detector
12: second flat panel detector
21: shell body
22: scintillation crystal array
23: light detector
24: collimator
25: light guide device
31: detected object
32: focus of disease
Detailed Description
Example embodiments will now be described more fully with reference to the accompanying drawings. Example embodiments may, however, be embodied in many different forms and should not be construed as limited to the embodiments set forth herein; rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the concept of example embodiments to those skilled in the art. The same reference numerals denote the same or similar structures in the drawings, and thus detailed descriptions thereof will be omitted.
Furthermore, the described features, structures, or characteristics may be combined in any suitable manner in one or more embodiments. In the following description, numerous specific details are provided to give a thorough understanding of embodiments of the disclosure. One skilled in the relevant art will recognize, however, that the embodiments of the disclosure can be practiced without one or more of the specific details, or with other methods, components, materials, and so forth. In other instances, well-known structures, materials, or operations are not shown or described in detail to avoid obscuring aspects of the disclosure.
Fig. 1 is a schematic structural diagram of a flat PET detector device in the prior art, which includes two large-area flat gamma-ray detectors, i.e., a first flat detector 11 and a second flat detector 12, which are oppositely disposed in the figure; fig. 2 is a schematic structural diagram of a flat panel detector shown in fig. 1. The working principle of the flat plate type PET detection device is as follows: the radioactive tracer drug labeled with the positive electron nuclide is injected into the object 31 to be detected, the positive electron nuclide decays to emit positrons, and annihilates with negative electrons in the object 31 to generate two gamma photons with opposite directions, so that the gamma photons are respectively detected by the photodetectors 23 in the two flat panel detectors holding the object 31 to be detected. The line of response 10 (LOR) in fig. 1 is the line between the photodetectors 23 that detect the two gamma photons. After a number of such annihilation reactions and lines of response 10 are recorded, a radiotracer activity map can be obtained by image reconstruction to obtain the location of the lesion 32.
As shown in fig. 3, is a schematic structural diagram of a PET detecting apparatus having single photon emission imaging function in the present exemplary embodiment; it also comprises two large-area flat-panel gamma-ray detectors, namely a first flat-panel detector 11 and a second flat-panel detector 12, which are arranged opposite to each other in the figure. As shown in fig. 4, a schematic structural diagram of the first flat panel detector 11 and/or the second flat panel detector 12 in fig. 3 is shown, which mainly includes a detector housing 21, a collimator 24, a scintillation detection mechanism, and the like.
Wherein, the scintillation detection mechanism is used for detecting incident gamma photons and is arranged in the detector shell 21; the collimator 24 is suitable for single photon imaging and is arranged on a light receiving surface of the flicker detection mechanism, and the collimator 24 can move relative to the light receiving surface of the flicker detection mechanism so as to face the light receiving surface of the flicker detection mechanism or stagger the light receiving surface of the flicker detection mechanism.
In the present exemplary embodiment, the collimator 24 is movable on the light receiving surface of the scintillation detection mechanism of the flat panel detector, so that a single photon emission imaging function can be realized when the collimator 24 faces the light receiving surface of the scintillation detection mechanism, and a positron emission imaging function can be realized when the collimator 24 deviates from the light receiving surface of the scintillation detection mechanism, thereby improving the use efficiency of the PET detection device by one machine with multiple purposes.
Next, a detailed description will be given of a possible specific implementation of the PET detection apparatus having single photon emission imaging function in the present exemplary embodiment.
As shown in fig. 3, in the present exemplary embodiment, the first flat panel detector 11 and the second flat panel detector 12 are the same, that is, the light receiving surfaces of the scintillation detection mechanisms of the first flat panel detector 11 and the second flat panel detector 12 are both provided with movable collimators 24. Therefore, when the single photon emission imaging function is realized, two groups of different data can be acquired for imaging, and the efficiency and accuracy of single photon emission imaging are improved. In a specific detection process, the first flat panel detector 11 and the second flat panel detector 12 may be disposed parallel to each other or at a predetermined angle according to different requirements, which is not particularly limited in this exemplary embodiment.
The collimator 24 in the present exemplary embodiment may have different implementations depending on different classification methods. For example, the collimator 24 may include a low energy collimator, a medium energy collimator, or a high energy collimator for different single photon species, or the like; it may also be a collimator comprising parallel holes for different collimation methods, a fan collimator, a pinhole collimator or a rotating plate collimator, etc.
In order to realize the movement of the collimator 24, the PET detecting apparatus having the single photon emission imaging function in the present exemplary embodiment further includes a driving mechanism and a control mechanism (not shown in the drawings). Wherein, the driving mechanism is used for driving the collimator 24 to move relative to the light receiving surface of the scintillation detection mechanism; the control mechanism is used for triggering the driving mechanism to drive the collimator 24 to move relative to the light receiving surface of the flicker detection mechanism. Specifically, the drive mechanism and the control mechanism may be purely mechanical or electrical, and are not particularly limited in the present exemplary embodiment.
In addition, in order to facilitate and guide and limit the movement of the collimator 24 relative to the light receiving surface of the scintillation detection mechanism, in the present exemplary embodiment, a sliding slot is further provided on the detector housing 21, and a sliding rail adapted to the sliding slot is correspondingly provided on the corresponding collimator 24; or, a slide rail is arranged on the detector housing 21, and a sliding groove adapted to the slide rail is correspondingly arranged on the collimator 24. By the cooperation of the slide rails and the slide grooves, the collimator 24 can be conveniently moved relative to the light receiving surface of the scintillation detection mechanism, and the movement can be guided and limited.
The flicker detection mechanism is formed by splicing a plurality of flicker detection modules; as shown in fig. 5, the scintillation detection mechanism adopts 35 scintillation detector modules to form a 5 × 7 array scintillation detection mechanism by seamless splicing, and the detector area can reach 160mm × 224mm, that is, the requirement of breast imaging can be met.
As shown in fig. 6, each of the scintillation detection modules includes a scintillation crystal array 22, a light guide 25, a photodetector 23, and a position logic circuit (not shown in the figure), among others.
The scintillation crystal array 22 is configured to receive incident gamma photons and emit scintillation light; in the present exemplary embodiment, the scintillation crystal array 22 may be composed of 16 × 16 LYSO scintillation crystals, the size of the LYSO scintillation crystals may be 1.9 × 15mm, and the gaps between the scintillation crystals may be filled with a high-reflectivity light-blocking material with a thickness of 0.1 mm; thus the peripheral dimensions of each detector module are 32mm x 32 mm. Of course, other types of scintillation crystals may be used for the scintillation crystal array 22, such as LaBr3 scintillation crystals, YSO scintillation crystals, YAP scintillation crystals, GSO scintillation crystals, or BGO scintillation crystals, among others.
A first end of the light guide 25 is connected to the scintillator crystal array 22; the second end is connected to an input of the photodetector 23 so as to pass the light signal received by the scintillation crystal to the photodetector 23. In the present exemplary embodiment, the light guide 25 may be a tapered light guide or the like.
The photodetector 23 has an input connected to a second end of the light guide 25 and an output connected to the position logic circuit, so that the received optical signal is converted into an electrical signal and then transmitted to the position logic circuit. In the present exemplary embodiment, the photodetector 23 may include a photomultiplier tube or a silicon photomultiplier tube; for example, a position-sensitive photomultiplier tube of the type R8900U-00-C12 from HAMAMATSU may be included.
The position logic circuit is connected with the output end of the optical detector 23 and the computer device, so that the position, time and energy information of the gamma ray extracted according to the received electric signal is transmitted to the computer device for image reconstruction.
Next, the detection method will be further described by taking the PET detector having the single photon emission imaging function as a PET detector dedicated to the mammary gland as an example.
When positron emission imaging is performed, the first flat panel detector 11 and the second flat panel detector 12 can be placed in parallel and opposite to each other and hold a measured object 31 such as a breast, and at this time, the collimator 24 staggers the light receiving surface of the scintillation detection mechanism, so that a scintillation crystal firstly reacts with a gamma ray and generates scintillation light, the scintillation light is transmitted to the photodetector 23 through the light guide device 25 and is converted into an electric signal, and the position, time and energy information of the gamma ray is extracted through processing of the electric signal by the position logic circuit; and the computer equipment carries out coincidence imaging according to the corresponding position, time and energy information.
When single photon emission imaging is performed, the collimator 24 at the front end of the first flat panel detector 11 and the second flat panel detector 12 can face the light receiving surface of the scintillation detection mechanism; because of the limitation of the collimator 24, the gamma ray can only enter the scintillation detection mechanism according to a specified path and act with the scintillation crystal to generate scintillation light, the scintillation light is also transmitted to the optical detector 23 through the optical guide device 25 and converted into an electric signal, and the position, time and energy information of the gamma ray is extracted through the processing of the electric signal by the position logic circuit; and the computer equipment carries out coincidence imaging according to the corresponding position, time and energy information.
In addition, when single photon emission imaging is performed, the first flat panel detector 11 and the second flat panel detector 12 may hold a measured portion such as a breast in a combination of various angles according to different requirements, for example, as shown in fig. 3, 7, and 8. Because can obtain two sets of different data and image when realizing single photon emission formation of image function, consequently can promote single photon emission formation of image's efficiency and rate of accuracy, and then improve the detectable rate and the image quality of focus 32, reduce the medicine dose simultaneously and reduce the acquisition time to reduce the radiation risk that quilt surveyed person and operator received.
In summary, it can be seen that, in the PET detecting apparatus having a single photon emission imaging function according to the present exemplary embodiment, the movable collimator is disposed on the light receiving surface of the scintillation detecting mechanism of the flat panel detector, so that the single photon emission imaging function can be implemented when the collimator faces the light receiving surface of the scintillation detecting mechanism, the positron emission imaging function can be implemented when the collimator is staggered from the light receiving surface of the scintillation detecting mechanism, and the service efficiency of the PET detecting apparatus is improved by one machine for multiple purposes.
The present disclosure has been described in terms of the above-described embodiments, which are merely exemplary of the implementations of the present disclosure. It must be noted that the disclosed embodiments do not limit the scope of the disclosure. Rather, it is intended that all such alterations and modifications be included within the spirit and scope of this disclosure.
Claims (10)
1. A PET detection device with single photon emission imaging function comprises a first flat panel detector and a second flat panel detector; wherein at least one of the first and second flat panel detectors comprises:
a probe housing;
the scintillation detection mechanism is arranged in the detector shell and used for detecting incident gamma photons;
the collimator is arranged on the light receiving surface of the scintillation detection mechanism;
the collimator is suitable for single photon imaging and can move relative to the light receiving surface of the scintillation detection mechanism so as to face the light receiving surface of the scintillation detection mechanism or stagger the light receiving surface of the scintillation detection mechanism.
2. The PET detection device with single photon emission imaging function of claim 1 wherein the first flat panel detector and the second flat panel detector are the same.
3. The PET detection device with the single photon emission imaging function according to claim 1, wherein a sliding groove is arranged on the detector housing, and a sliding rail adapted to the sliding groove is correspondingly arranged on the collimator; or, a slide rail is arranged on the detector shell, and a sliding groove matched with the slide rail is correspondingly arranged on the collimator.
4. The PET detection device with single photon emission imaging function according to claim 1, further comprising:
the driving mechanism is used for driving the collimator to move relative to the light receiving surface of the flicker detection mechanism;
and the control mechanism is used for triggering the driving mechanism to drive the collimator to move relative to the light receiving surface of the flicker detection mechanism.
5. The PET detection device with single photon emission imaging function of claim 1 wherein the first flat panel detector and the second flat panel detector are parallel or at a predetermined angle.
6. The PET detection device with single photon emission imaging function according to claim 1 wherein said collimator comprises: a low energy collimator, a medium energy collimator, or a high energy collimator; or,
the collimator includes: a parallel-hole collimator, a fan collimator, a pinhole collimator, or a rotating plate collimator.
7. The PET detection device with single photon emission imaging function of claim 1 wherein the scintillation detection mechanism is composed of a plurality of scintillation detection modules which are spliced together; each of the flicker detection modules includes:
a scintillation crystal array for receiving incident gamma photons and emitting scintillation light;
a light guide device having a first end connected to the array of scintillation crystals;
a light detector, the input end of which is connected with the second end of the light guide device; and the number of the first and second groups,
and the position logic circuit is connected with the output end of the light detector.
8. The PET detection device with single photon emission imaging of claim 7 wherein the scintillation crystals in the array of scintillation crystals comprise: LYSO scintillation crystals, LaBr3 scintillation crystals, YSO scintillation crystals, YAP scintillation crystals, GSO scintillation crystals, or BGO scintillation crystals.
9. The PET detection device with single photon emission imaging function of claim 7 wherein the light guide device is a tapered light guide.
10. The PET detection device with single photon emission imaging of claim 7 wherein the light detector comprises a photomultiplier tube or a silicon photomultiplier tube.
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