CN113081018B - PET medical imaging system - Google Patents
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Abstract
The application relates to a PET medical imaging system comprising: the detector is accommodated in the rack and comprises a plurality of annular detection units which are axially arranged, and each annular detection unit comprises a plurality of detector modules which are composed of crystals; the annular detection unit acquires first scanning data in a first time, acquires second scanning data in a time subset in the first time, and the first scanning data and the second scanning data comprise cross coincidence data commonly detected by different annular detection units; the image reconstruction unit performs image reconstruction based on the second scan data to obtain a second PET image. The application can solve the problem that the long-axis PET medical imaging system cannot preview images in the data acquisition process.
Description
Technical Field
The application relates to the technical field of medical imaging, in particular to a PET medical imaging system.
Background
PET (Positron Emission Tomography ) has important application value in the field of medical imaging as a biomedical research technology and clinical diagnostic means. PET is one of the best ways to realize molecular level imaging, and provides a very favorable analysis means for clinical diagnosis, treatment, prognosis detection and development of new drugs.
In the field of clinical diagnosis, functional imaging of tissues and organs with different metabolic properties by PET is often used for diagnosis of diseases. In clinical scanning, a technician or doctor needs to determine the imaging effect and the diagnostic effect from the image, and determine whether additional scanning is required for the patient. Therefore, the need to see the image of the patient as soon as possible is a truly urgent clinical need.
As shown in fig. 1, short axis PET medical imaging systems have a short axial field of view and typically require a split bed scan to achieve full body coverage of the scanned subject. Generally, each bed scan takes about 1 to 3 minutes, and at the end of the second bed 102 scan, an image of the first bed 101 has been reconstructed; at the end of the third bed 103 scan, an image of the second bed 102 has been reconstructed; at the end of the fourth bed 104 scan, an image of the third bed 103 has been reconstructed. Therefore, at the end of the scan, only one to two images of the bed are left, and at this time, the images of the most part of the human body can be seen, so that the doctor or technician can make a judgment. As shown in fig. 2, the long-axis PET medical imaging system (the single-bed axial scanning range is greater than 0.5 m) can obtain the whole images of a plurality of parts of the body and even the whole body by only scanning the single-bed, so that the image can not be previewed in the data acquisition process.
Disclosure of Invention
The embodiment of the application provides a PET medical imaging system, which at least solves the problem that a long-axis PET medical imaging system in the related art cannot preview images in the data acquisition process.
The PET medical imaging system provided by the embodiment of the application comprises: a gantry, a detector and an image reconstruction unit, wherein,
the detector is accommodated in the rack and comprises a plurality of annular detection units which are axially arranged, and each annular detection unit comprises a plurality of detector modules which are composed of crystals;
the annular detection unit acquires first scanning data in a first time, acquires second scanning data in a time subset in the first time, and the first scanning data and the second scanning data comprise cross coincidence data commonly detected by different annular detection units;
the image reconstruction unit performs image reconstruction based on the second scan data to obtain a second PET image.
In some of these embodiments, the time starting point of the subset of times coincides with the time starting point of the first time.
In some of these embodiments, the length of the first time and/or the subset of times is set according to the system sensitivity of the PET medical imaging system.
In some embodiments, the image reconstruction unit reconstructs the first scan data to obtain a first PET image.
In some of these embodiments, the imaging system further comprises a processor that generates a cue signal from the second PET image, the cue signal being used to cue the operator whether rescanning or additional delay scanning of the scanned object is required.
In some embodiments, when the processor receives the rescanning instruction, the detector acquires third scan data, and the image reconstruction unit reconstructs according to the third scan data to obtain a third PET image.
In some embodiments, the image reconstruction unit reconstructs the physically corrected third scan data to obtain a third PET image.
In some embodiments, when the processor receives the additional delay scanning instruction, the detector acquires fourth scanning data, and the image reconstruction unit reconstructs according to the fourth scanning data to obtain a fourth PET image.
In some embodiments, the image reconstruction unit reconstructs the fourth scan data after the physical correction to obtain a fourth PET image.
In some of these embodiments, the physical correction includes at least one of attenuation correction, scattering correction, random correction.
Compared with the related art, the PET medical imaging system provided by the embodiment of the application has the advantages that the detector is accommodated in the scanning cavity and comprises a plurality of annular detection units which are axially arranged, the first scanning data and the second scanning data comprise the cross coincidence data detected by different annular detection units together, and the image reconstruction is carried out based on the second scanning data acquired in a time subset in the first time so as to acquire a second PET image. Based on the system, the rapid reconstruction of medical images can be realized in a single-bed scanning process of the long-axis PET medical imaging system based on partial original scanning data in the time subset in the data acquisition and reconstruction process, so that three-dimensional images which are enough to meet the clinical preview requirement of doctors are produced, and the image preview of the long-axis PET medical imaging system in the data acquisition process is realized.
The details of one or more embodiments of the application are set forth in the accompanying drawings and the description below to provide a more thorough understanding of the other features, objects, and advantages of the application.
Drawings
The accompanying drawings, which are included to provide a further understanding of the application and are incorporated in and constitute a part of this specification, illustrate embodiments of the application and together with the description serve to explain the application and do not constitute a limitation on the application. In the drawings:
FIG. 1 is a schematic view of a split-bed scanning process of a short axis PET medical imaging system in one embodiment of the application;
FIG. 2 is a schematic diagram of a single bed scanning process of a long axis PET medical imaging system in one embodiment of the application;
FIG. 3 is a schematic diagram of the structure of a PET medical imaging system in one embodiment of the application;
fig. 4 is a schematic diagram of the structure of a PET medical imaging system in another embodiment of the present application.
Description of the drawings: 101. a first bed; 102. a second bed; 103. a third bed; 104. a fourth bed; 201. a scanning chamber; 202. a detector; 203. an image reconstruction unit; 204. a processor; 205. a memory; 206. an input unit; 2061. a touch panel; 2062. other input devices; 207. a display unit; 2071. a display panel.
Detailed Description
The present application will be described and illustrated with reference to the accompanying drawings and examples in order to make the objects, technical solutions and advantages of the present application more apparent. It should be understood that the specific embodiments described herein are for purposes of illustration only and are not intended to limit the scope of the application. All other embodiments, which can be made by a person of ordinary skill in the art based on the embodiments provided by the present application without making any inventive effort, are intended to fall within the scope of the present application.
It is apparent that the drawings in the following description are only some examples or embodiments of the present application, and it is possible for those of ordinary skill in the art to apply the present application to other similar situations according to these drawings without inventive effort. Moreover, it should be appreciated that while such a development effort might be complex and lengthy, it would nevertheless be a routine undertaking of design, fabrication, or manufacture for those of ordinary skill having the benefit of this disclosure, and thus should not be construed as having the benefit of this disclosure.
Reference in the specification to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment may be included in at least one embodiment of the application. The appearances of such phrases in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. It is to be expressly and implicitly understood by those of ordinary skill in the art that the described embodiments of the application can be combined with other embodiments without conflict.
Unless defined otherwise, technical or scientific terms used herein should be given the ordinary meaning as understood by one of ordinary skill in the art to which this application belongs. The terms "a," "an," "the," and similar referents in the context of the application are not to be construed as limiting the quantity, but rather as singular or plural. The terms "comprising," "including," "having," and any variations thereof, are intended to cover a non-exclusive inclusion; for example, a process, method, system, article, or apparatus that comprises a list of steps or modules (elements) is not limited to only those steps or elements but may include other steps or elements not expressly listed or inherent to such process, method, article, or apparatus. The terms "connected," "coupled," and the like in connection with the present application are not limited to physical or mechanical connections, but may include electrical connections, whether direct or indirect. The term "plurality" as used herein means two or more. "and/or" describes an association relationship of an association object, meaning that there may be three relationships, e.g., "a and/or B" may mean: a exists alone, A and B exist together, and B exists alone. The character "/" generally indicates that the context-dependent object is an "or" relationship. The terms "first," "second," "third," and the like, as used herein, are merely distinguishing between similar objects and not representing a particular ordering of objects.
Positron Emission Tomography (PET) is a noninvasive medical imaging technology for detecting metabolic characteristics of organs of human bodies or animals, and has the characteristics of high sensitivity, good accuracy and accurate positioning. In PET imaging, a radioactive drug capable of emitting positrons is injected into a living body, the positrons annihilate with electrons in the living body to generate two gamma photons with opposite directions and 511keV energy, the photons are detected by detectors surrounding the living body to be detected, information of the photons is stored in a manner of coincidence counting, and raw data can be reconstructed into a tomographic image of the concentration distribution of the radionuclide in the living body to be detected through an image reconstruction algorithm, so that a powerful analysis means is provided for clinical diagnosis, treatment and prognosis monitoring.
The PET medical imaging system related to the application can be used for non-invasive imaging, such as diagnosis and research of diseases, industrial fields and the like, and can be a single imaging system or a combination of a plurality of different imaging systems. For example, a positron emission computed tomography system (PET system), a positron emission computed tomography-computed tomography multi-modality system (PET-CT system), a positron emission computed tomography-magnetic resonance multi-modality hybrid system (PET-MR system), or the like may be included.
Embodiments of the present application will be described below with respect to a PET medical imaging system.
The present embodiment provides a PET medical imaging system. Illustratively, FIG. 3 is a block diagram of a PET medical imaging system in accordance with an embodiment of the present application. As shown in fig. 3, the PET medical imaging system includes: a scanning chamber 201, a detector 202 and an image reconstruction unit 203.
In this embodiment, the detector is accommodated in a gantry and includes a plurality Of annular detection units arranged in an axial direction, specifically, a cylindrical scan cavity 201 is disposed on the gantry, and the detector 202 is accommodated in the scan cavity 201 and includes a plurality Of annular detection units arranged in an axial direction, so as to form a PET medical imaging system (hereinafter referred to as a long axis PET system) having a long axis Field Of View (FOV). For long axis PET systems, the axial length of the scanning aperture is typically greater than 0.5m, which can enable scanning imaging of multiple sites, or even whole-body images, of a scanned object within the scanning aperture during a single bed scan. Optionally, the PET imaging system includes two, three, four or more annular detection units providing radiation detection, the subject being movable with the scanning bed into a detection region enclosed by the plurality of annular detection units for scanning.
Wherein each annular detection unit comprises a plurality of detector modules consisting of crystals. Illustratively, each annular-shaped detection unit includes more than four detector modules, each of which may include a crystal array, a photoelectric conversion assembly, and a processing circuit connected in sequence. In an alternative example, the processing circuitry may be Data Acquisition (DAQ) system circuitry, which may include sub-circuitry that implements different functions, such as front-end Data Acquisition circuitry. The detector module detects the pair annihilation gamma rays emitted from the inside of a subject, converts the detected gamma photons into optical signals, and transmits the optical signals to the photoelectric conversion assembly, the photoelectric conversion assembly converts the optical signals into electrical signals, and then transmits the electrical signals to the processing circuit, and the processing circuit converts the electrical signals into pulse signals and can output the information of the pulse signals.
Generally, during a PET scan, a positron emitted by a radionuclide, after moving about 1mm in the body, combines with a negative electron in tissue to generate annihilation radiation (i.e., annihilation event) that generates two gamma photons of equal energy and opposite direction. Due to the different path of the two gamma photons within the scanning cavity 201, there is also a certain difference in the time to reach the two annular detection units. If two photons 180 degrees from each other are detected by the ring detector units located on the response line within a prescribed time window, a coincidence event is formed. And obtaining coincidence data corresponding to the coincidence event by carrying out coincidence processing on the output data of the at least one annular detection unit. For a PET medical imaging system comprising a plurality of annular detection units, different annular detection units respectively receive one of a pair of gamma photons to respectively form single events, coincidence events formed by two single events through coincidence circuits are cross coincidence events, and a data set formed by the cross coincidence events is cross coincidence data.
In this embodiment, the annular detection unit acquires first scan data in a first time, where the first scan data is raw PET projection data obtained by PET scanning of a scan object. Because the long-axis PET system has large data acquisition amount during single-bed scanning, the image acquisition time is often as long as 3min. In order to meet the rapid mapping requirement in clinical judgment, the second scanning data can be acquired in a time subset in the first time for image reconstruction. The first scanning data and the second scanning data comprise cross coincidence data obtained by coincidence processing of output data of different annular detection units which are axially arranged. Wherein the subset of times includes any scanning period of time within the first time. In some of these embodiments, the time start of the subset of times coincides with the time start of the first time, and the time end of the subset of times is earlier than the time end of the first time. In some of these embodiments, the time end of the subset of times coincides with the time end of the first time, and the time start of the subset of times is later than the time start of the first time. In some of these embodiments, the time start and time end of the subset of times are not consistent with the time start and time end of the first time. The second scan data includes a portion of the first scan data.
The image reconstruction unit 203 performs image reconstruction and display on the spatial distribution of the contrast agent in the subject in the detection region by using a reconstruction algorithm according to the true coincidence event obtained from the coincidence data corresponding to the coincidence event, and obtains a PET image. In some embodiments, the image reconstruction unit 203 may reconstruct the coincidence event data by algorithms such as filtered back projection (Filtered Back Projection, FBP), maximum expected reconstruction (Expectation Maximization, EM), maximum a posteriori reconstruction (Maximum A Posteriori, MAP) and the like to obtain a PET (activity) image. By way of example, the image reconstruction unit 203 may comprise a memory, a processor, and computer instructions stored on the memory, which when executed by the processor, perform medical image reconstruction. The computer instructions may be stored permanently in a computer-storage medium or may be implemented after being temporarily acquired from a network via a communication port. The processor may be a general purpose processor (CPU) or a Graphics Processor (GPU).
In summary, in the PET medical imaging system provided by the embodiment of the present application, the detector is accommodated in the scanning cavity and includes a plurality of annular detection units arranged axially, the first scan data and the second scan data include cross coincidence data detected by different annular detection units together, and image reconstruction is performed based on the second scan data acquired in a time subset in the first time, so as to obtain a second PET image. Based on the system, the rapid reconstruction of medical images can be realized in a single-bed scanning process of the long-axis PET medical imaging system based on partial original scanning data in the time subset in the data acquisition and reconstruction process, so that three-dimensional images which are enough to meet the clinical preview requirement of doctors are produced, and the image preview of the long-axis PET medical imaging system in the data acquisition process is realized.
The embodiments of the present application will be described and illustrated below by means of preferred embodiments.
For a short-axis PET medical imaging system, generally, only one annular detection unit is provided, the axial scanning visual field range is limited to about 25 centimeters, the coincidence judgment and selection among the detector data in one annular detection unit can be only processed, the synchronous coincidence and cross coincidence processing of a plurality of annular detection units can not be completed, the system sensitivity is poor, and the efficiency is low. The long-axis PET medical imaging system greatly improves the coincidence counting rate, coincidence detection processing capacity and system sensitivity due to the expansion of the scanning visual field, the first scanning time and the second scanning time are influenced by the system sensitivity, and the higher the sensitivity is, the shorter the acquisition time is required for producing images. The length of the first time and/or the time subset can be adaptively set according to the system sensitivity of the PET medical imaging system, and for different imaging systems or different clinical diagnosis conditions of the same imaging system, the length of different first time and/or time subset can be set, so that the differentiated setting of the scanning parameters of the PET medical imaging system is realized, and the personalized clinical requirements of doctors are met. In particular, the higher the sensitivity the shorter the length of the first scan time and the time subset can be set, and vice versa.
On the basis of the above embodiments, in some of these embodiments, the time start point of the subset of times coincides with the time start point of the first time, and the time end point of the subset of times is earlier than the time end point of the first time. The scheme of the embodiment can preview the second PET image in the shortest time after the scanning starts on the premise that the lengths of the time subsets are the same. During the scanning, image reconstruction may be performed immediately after the second scan data is acquired within the temporal subset. Thus, the second PET image can be quickly produced for the doctor to preview without waiting for the scanning to be completed. The second PET image can be used for pre-judging whether the final reconstructed image of the scanned object meets clinical requirements, such as judging whether the scanning range is proper, whether the image quality meets requirements, and the like. In some of these embodiments, when the length of the time subset is 15s or more, it may be ensured that a second image meeting clinical judgment requirements is produced with a sufficient amount of data.
In some of these embodiments, the scanning time of the long axis PET medical imaging system is ≡2min, and the subset of times includes any 15s-30s time period selected from 0-30 s. When the data in the time subset is selected for reconstruction, the reconstruction of the first scanning data is not required to be completed, the second PET image can be quickly reconstructed before the scanning process is completed, and the acquisition of enough data quantity is ensured to obtain the image quality which meets expectations, so that a doctor can preview the image reconstruction result according to the second PET image conveniently.
In some of these embodiments, data bias is caused by the fact that the transmission and reception of photons during data acquisition is affected by physical factors such as scattering effects, attenuation effects, dead time effects, random coincidence, detector efficiency, etc. By intercepting the second scan data of a subset of the first time, the image reconstruction unit 203 reconstructs the second scan data after the physical correction, so that a three-dimensional preview image with higher quality including the physical correction process can be quickly reconstructed.
Radiopharmaceuticals for PET imaging can be classified into long half-life medicines and short half-life medicines. Among them, long half-life drugs have a slow rate of drug dose reduction after being injected into the human body because of a long half-life (several hours, several days, even several tens of days), and can exist in the human body for a long time, and only the dose can be reduced in order to ensure the safety of patients when using such drugs. However, since the short half-life drug has a short half-life (several tens of minutes, several minutes), the dose of the drug decreases rapidly after injection into the human body, and in order to secure a certain imaging quality, a higher dose is usually injected at the initial stage of scanning, and a sufficient scanning time is secured. Otherwise, after two or three half-lives, the desired image quality may not be obtained according to the conventional image reconstruction method.
In some embodiments, when the scan time of the PET medical imaging system is long, the second PET image previews the reconstructed image result, and further scan operations may be performed according to the previewed result, for example, to determine whether to perform positioning adjustment on the scanned object, whether to add delay scanning, whether to perform rescanning, and so on.
In some embodiments, if the image quality of the second PET image meets the clinical requirement, the reconstruction is directly performed according to the first scan data, so as to obtain the first PET image. The reconstructed first PET image may be directly used as a basis and foundation for diagnosis.
In some of these embodiments, the imaging system further includes a processor 204, the processor 204 generating a cue signal from the second PET image. The processor 204 may be comprised of one or more processors, may include a Central Processing Unit (CPU), or an application specific integrated circuit (Application Specific Integrated Circuit, abbreviated as ASIC), or may be configured to implement one or more integrated circuits of embodiments of the present application. The prompting signal is used for prompting an operator whether to re-scan or add delay scanning to the scanned object, and the prompting information can be interface characters, sound or video.
As shown in fig. 4, in some of these embodiments, a memory 205, an input unit 206 and a display unit 207 are also included, which are connected to the processor 204. It will be appreciated by those skilled in the art that the PET medical imaging system configuration shown in FIG. 4 is not limiting of the PET medical imaging system and may include more or fewer components than shown, or certain components may be combined, or a different arrangement of components.
The memory 205 may be used to store software programs and modules, and the processor 204 may execute various functional applications and data processing of the user terminal by executing the software programs and modules stored in the memory 205. Memory 205 may be used to store or cache various data files that need to be processed and/or communicated, as well as possible computer program instructions for execution by processor 204. The memory 205 may mainly include a storage program area that may store an operating system, application programs required for at least one function (such as a sound playing function, an image playing function, etc.), and a storage data area; the storage data area may store data (such as scan data, etc.) created according to the use of the user terminal, etc. In addition, the memory 205 may include high-speed random access memory 205, and may also include non-volatile memory 205, such as at least one disk memory 205 device, flash memory device, or other volatile solid-state memory 205 device. In some embodiments, the controller may include one or a combination of several of a central processing unit (Central Processing Unit, CPU), application specific integrated circuit (Application Specific Integrated Circuit, ASIC), special instruction processor (Application Specific Instruction Set Processor, ASIP), physical processor (Physics Processing Unit, PPU), digital signal processor (Digital Processing Processor, DSP), field programmable gate array (Field-Programmable Gate Array, FPGA), programmable logic device (Programmable Logic Device, PLD), microprocessor, controller, microcontroller, or the like.
The input unit 206 may be a keyboard, a mouse, a control box, etc., and supports input/output of corresponding data streams. The input unit 206 may be used to receive input numeric or character information and to generate key signal inputs related to user settings and function control. In particular, the input sheet may include a touch panel 2061 and other input devices 2062. The touch panel 2061, also referred to as a touch screen, may collect touch operations thereon or thereabout by a user (such as operations of the user on the touch panel 2061 or thereabout by using any suitable object or accessory such as a finger, a stylus pen, or the like) and drive the corresponding connection device according to a predetermined program. Alternatively, the touch panel 2061 may comprise two parts of a touch detection device and a touch controller. The touch detection device detects the touch azimuth of a user, detects a signal brought by touch operation and transmits the signal to the touch controller; the touch controller receives touch information from the touch detection device and converts it into touch point coordinates, which are then sent to the processor 204, and can receive commands from the processor 204 and execute them. Further, the touch panel 2061 may be implemented in various types such as a resistive type, a capacitive type, an infrared type, and a surface acoustic wave type. The input unit 206 may include other input devices 2062 in addition to the touch panel 2061. In particular, other input devices 2062 may include, but are not limited to, one or more of a physical keyboard, function keys (e.g., volume control keys, switch keys, etc.), a trackball, a mouse, a joystick, etc.
The display unit 207 may be used to display information input by a user or information provided to the user and various menus of the user terminal. The display unit 207 may include a display panel 2071, and alternatively, the display panel 2071 may be configured in the form of a liquid crystal display (Liquid Crystal Display, abbreviated as LCD), an Organic Light-Emitting Diode (OLED), or the like. Further, the touch panel 2061 may cover the display panel 2071, and when the touch panel 2061 detects a touch operation thereon or nearby, the touch operation is transmitted to the processor 204 to determine the type of the touch event, and then the processor 204 provides a corresponding visual output on the display panel 2071 according to the type of the touch event. The touch panel 2061 and the display panel 2071 are two independent components for implementing the input and output functions of the user terminal, but in some embodiments, the touch panel 2061 may be integrated with the display panel 2071 to implement the input and output functions of the user terminal.
In some of these embodiments, if the image quality of the second PET image does not meet the clinical requirement, the processor 204 generates a cue signal from the second PET image, the cue signal being used to alert the operator as to whether rescanning the scanned object is required.
In some embodiments, when the processor 204 receives the rescanning instruction, the detector acquires third scan data, and the image reconstruction unit 203 reconstructs a third PET image according to the third scan data. Specifically, when the operator determines that the second PET image needs to be scanned, the processor 204 performs rescanning according to the received rescanning instruction, so as to obtain third scan data. The third scan data may be secondary scan data obtained by rescanning after adjustment of the scan object positioning, adjustment of physiological factors, adjustment of hardware and scan parameters. By judging the preview image according to the second PET image, the scanning operation can be timely adjusted, and the scanning efficiency is improved. In a preferred embodiment, the image reconstruction unit 203 reconstructs the physically corrected third scan data to obtain a third PET image.
Wherein the physical correction includes at least one of attenuation correction, scattering correction, random correction. Where random coincidence refers to photons from different annihilation times being detected simultaneously within a coincidence time window and recorded as a coincidence event, random correction can be made by setting the coincidence time window. Attenuation correction refers to the phenomenon that photons are scattered or absorbed by tissues when flying in a medium, and the attenuation is compensated to obtain quantitative analysis images. The most common way of attenuation correction is to reconstruct the attenuation map after transmission scanning, or to a priori divide the specific tissue by image segmentation techniques. For example: in one embodiment, performing the attenuation correction on the second scan data may include the steps of: acquiring an anatomical image corresponding to a scanned object, wherein the anatomical image can be an anatomical image such as a CT image, an MR image and the like, and the anatomical image can contain classification information of a plurality of tissues such as lung, fat, rib, spine, heart and the like; registering the second PET image to the anatomical image, and distributing corresponding attenuation values to voxels of the PET image according to classification information of a plurality of tissues to obtain an attenuation map; and performing attenuation correction during reconstruction of the scatter-corrected second scan data into a second PET image of the scan object based on the attenuation map. Of course, in other embodiments, the second scan data may also be normalized. The normalization correction refers to that in the PET imaging process, due to factors such as geometric structures, hardware performance and the like, detection efficiency of detectors at different positions in a detection system is often inconsistent, data distortion is further caused, and artifacts are generated on a finally formed image. A method for eliminating the difference in detection efficiency between individual channels of a detector. It will be appreciated that the physical correction method may also include other physical corrections such as dead time correction, and the present application is not limited in particular.
In some embodiments, if the image quality of the second PET image does not meet the clinical requirement, the processor 204 generates a prompt signal from the second PET image, the prompt signal being used to prompt the operator if additional delayed scanning of the scan object is required.
Based on the above embodiments, in some embodiments, after the processor 204 receives the additional delay scan command, the detector stops acquiring the scan data, uses the completed scan data as the first scan data, and resumes acquiring the fourth scan data after the detector stops scanning the scan data, and the image reconstruction unit 203 reconstructs according to the fourth scan data to obtain a fourth PET image.
In some embodiments, the processor 204 receives the additional delayed scan instruction and the detector continues to complete acquisition of the first scan data, reconstructing the first PET image from the first scan data. And starting to acquire fourth scanning data at a time point after the acquisition of the first scanning data is completed, and reconstructing a fourth PET image according to the fourth scanning data. To ensure image quality, the time point is spaced from the time point at which the first scan data is completed by no more than 30 minutes.
In some embodiments, when the operator determines that the additional delay scan is required according to the second PET image, the processor 204 performs the additional scan according to the received additional delay scan instruction, and integrates the additional scan data obtained based on the first scan data and the additional scan data to obtain fourth scan data. The fourth scan data may be scan data obtained by adding scan data to the first scan data according to predetermined scan parameters, positioning, and other information. By judging the preview image according to the second PET image, whether the first scanning data are available or not can be confirmed in time, and whether the scanning operation needs to be adjusted or not can be confirmed.
On the basis of the above-described embodiments, in some of these embodiments, when the operator determines from the second PET image that no re-scan is required and no additional delayed scan is required, indicating that no adjustment of the scan operation is required, the image reconstruction unit 203 may reconstruct the first PET image based on the first scan data.
In some embodiments, the image reconstruction unit 203 may reconstruct the first scan data after the physical correction, to obtain a first PET image. The physical correction manner is the same as that of the above embodiment, and the description of the present application is omitted here. In other embodiments, the distribution of the drug does not change dramatically since the radiopharmaceutical in the subject is already in the drug equilibrium phase at the beginning of the PET scan. Therefore, when it is not necessary to perform a re-scan or to add a delay scan, in reconstructing the first PET image based on the first scan data, it is possible to multiplex the physical correction intermediate data (such as attenuation correction estimation, scatter correction estimation, and random correction estimation data) in the second PET image reconstruction process, reduce the calculation amount of the physical correction estimation at the time of diagnostic image reconstruction, and accelerate the reconstruction speed of the first PET image.
The technical features of the above-described embodiments may be arbitrarily combined, and all possible combinations of the technical features in the above-described embodiments are not described for brevity of description, however, as long as there is no contradiction between the combinations of the technical features, they should be considered as the scope of the description.
The above examples illustrate only a few embodiments of the application, which are described in detail and are not to be construed as limiting the scope of the application. It should be noted that it will be apparent to those skilled in the art that several variations and modifications can be made without departing from the spirit of the application, which are all within the scope of the application. Accordingly, the scope of protection of the present application is to be determined by the appended claims.
Claims (10)
1. A PET medical imaging system comprising: a gantry, a detector and an image reconstruction unit, characterized in that,
the detector is accommodated in the rack and comprises a plurality of annular detection units which are axially arranged, and each annular detection unit comprises a plurality of detector modules which are composed of crystals;
the annular detection unit acquires first scanning data in a first time, acquires second scanning data in a time subset in the first time, and the first scanning data and the second scanning data comprise cross coincidence data commonly detected by different annular detection units;
the image reconstruction unit performs image reconstruction based on the second scan data to obtain a second PET image;
the PET medical imaging system is also used for,
pre-judging whether the scanning range of the final reconstructed image of the scanning object is suitable or not based on the second PET image; and/or; and judging whether the scanned object needs to be subjected to positioning adjustment or not based on the second PET image.
2. The PET medical imaging system of claim 1, wherein the temporal starting point of the temporal subset coincides with the temporal starting point of the first time.
3. The PET medical imaging system of claim 1, wherein the length of the first time and/or subset of times is set according to a system sensitivity of the PET medical imaging system.
4. The PET medical imaging system of claim 1, wherein the image reconstruction unit reconstructs the first scan data to obtain a first PET image.
5. The PET medical imaging system of claim 1, further comprising a processor that generates a cue signal from the second PET image, the cue signal for alerting an operator whether a rescan or an additional delay scan of the scanned object is required.
6. The PET medical imaging system of claim 5, wherein the processor, upon receiving a rescanning instruction, acquires third scan data from which the detector reconstructs, and wherein the image reconstruction unit obtains a third PET image.
7. The PET medical imaging system of claim 6, wherein the image reconstruction unit reconstructs the physically corrected third scan data to obtain a third PET image.
8. The PET medical imaging system of claim 5, wherein the processor, upon receiving the additional delayed scan instruction, acquires fourth scan data from which the image reconstruction unit reconstructs, resulting in a fourth PET image.
9. The PET medical imaging system of claim 8, wherein the image reconstruction unit reconstructs the fourth scan data after the physical correction to obtain a fourth PET image.
10. The medical imaging system of claim 7 or 9, wherein the physical correction comprises at least one of attenuation correction, scatter correction, random correction.
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Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105792754A (en) * | 2013-07-18 | 2016-07-20 | 通用电气公司 | Methods and systems for axially segmenting positron emission tomography data |
| CN109480883A (en) * | 2017-09-11 | 2019-03-19 | 佳能医疗***株式会社 | Medical diagnostic imaging apparatus |
| CN111402355A (en) * | 2020-03-19 | 2020-07-10 | 上海联影医疗科技有限公司 | PET image reconstruction method and device and computer equipment |
| CN111566745A (en) * | 2017-12-04 | 2020-08-21 | 皇家飞利浦有限公司 | Automated prompt Positron Emission Tomography (PET) scan planning and optimization |
| CN111568450A (en) * | 2020-05-20 | 2020-08-25 | 上海联影医疗科技有限公司 | PET scanning data scattering correction method and device and computer equipment |
| CN111833409A (en) * | 2020-06-29 | 2020-10-27 | 东软医疗***股份有限公司 | Image processing method and PET imaging system |
| CN112017258A (en) * | 2020-09-16 | 2020-12-01 | 上海联影医疗科技有限公司 | PET image reconstruction method, apparatus, computer device, and storage medium |
Family Cites Families (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20040195512A1 (en) * | 2000-05-16 | 2004-10-07 | Crosetto Dario B. | Method and apparatus for anatomical and functional medical imaging |
| US7381959B2 (en) * | 2005-08-17 | 2008-06-03 | General Electric Company | Technique for reconstructing PET scan images |
| US8000513B2 (en) * | 2008-09-22 | 2011-08-16 | Siemens Medical Solutions Usa, Inc. | System and method for 3D time of flight PET forward projection based on an exact axial inverse rebinning relation in fourier space |
| US8530846B2 (en) * | 2009-12-23 | 2013-09-10 | General Electric Company | Apparatus and methods for detector scatter recovery for nuclear medicine imaging systems |
| US10022097B2 (en) * | 2014-06-16 | 2018-07-17 | University Of Southern California | Direct patlak estimation from list-mode PET data |
| US11717184B2 (en) * | 2019-01-07 | 2023-08-08 | Siemens Medical Solutions Usa, Inc. | Tracking head motion for medical imaging |
-
2021
- 2021-03-31 CN CN202110348577.1A patent/CN113081018B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105792754A (en) * | 2013-07-18 | 2016-07-20 | 通用电气公司 | Methods and systems for axially segmenting positron emission tomography data |
| CN109480883A (en) * | 2017-09-11 | 2019-03-19 | 佳能医疗***株式会社 | Medical diagnostic imaging apparatus |
| CN111566745A (en) * | 2017-12-04 | 2020-08-21 | 皇家飞利浦有限公司 | Automated prompt Positron Emission Tomography (PET) scan planning and optimization |
| CN111402355A (en) * | 2020-03-19 | 2020-07-10 | 上海联影医疗科技有限公司 | PET image reconstruction method and device and computer equipment |
| CN111568450A (en) * | 2020-05-20 | 2020-08-25 | 上海联影医疗科技有限公司 | PET scanning data scattering correction method and device and computer equipment |
| CN111833409A (en) * | 2020-06-29 | 2020-10-27 | 东软医疗***股份有限公司 | Image processing method and PET imaging system |
| CN112017258A (en) * | 2020-09-16 | 2020-12-01 | 上海联影医疗科技有限公司 | PET image reconstruction method, apparatus, computer device, and storage medium |
Non-Patent Citations (1)
| Title |
|---|
| 每床位采集时间对18F-FDG PET图像质量和SUV值的影响;徐磊 等;中国医疗设备;第33卷(第11期);第28-32页 * |
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