JP2017086903A - Medical image diagnostic system, morphological image diagnostic apparatus, and nuclear medicine image diagnostic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a medical image diagnostic system, a morphological image diagnostic apparatus, and a nuclear medicine image diagnostic apparatus which reduce burden on an operator.SOLUTION: A medical image diagnostic system according to an embodiment is the one having a morphological image diagnostic apparatus and a nuclear medicine image diagnostic apparatus, and includes an acquisition part, a rack device, and a control device. The acquisition part acquires information on a position of a portion of a subject on the basis of a morphological image collected by the morphological image diagnostic apparatus. The rack device captures a nuclear medicine image of the subject. The control part controls the rack device on the basis of the information on the position of the portion and an imaging condition for each of a plurality of portions.SELECTED DRAWING: Figure 2

Description

  Embodiments described herein relate generally to a medical image diagnostic system, a morphological image diagnostic apparatus, and a nuclear medicine image diagnostic apparatus.

  2. Description of the Related Art In recent years, apparatuses that combine a functional image diagnostic apparatus and a morphological image diagnostic apparatus, such as a PET (Positron Emission Tomography) -CT (Computed Tomography) apparatus, are known.

  A medical image diagnostic system that combines a morphological image diagnostic apparatus and a functional image diagnostic apparatus performs, for example, scanning in a morphological image diagnostic apparatus to generate a positioning scan image, and an operator performs a scan based on the generated positioning scan image. The functional image diagnostic apparatus performs whole-body imaging according to the planned imaging plan.

  However, when performing whole body imaging, detailed imaging of a specific part, and detailed imaging of a plurality of parts at the same time in the functional image diagnostic apparatus, the operator confirms the imaging range and part with a positioning scan image, and for each imaging position. The acquisition time by the functional image diagnostic apparatus must be input. Therefore, the burden on the operator is large.

JP 2012-011181 A

  The problem to be solved by the embodiment is to provide a medical image diagnostic system, a morphological image diagnostic apparatus, and a nuclear medicine image diagnostic apparatus that can reduce the burden on the operator.

  A medical image diagnostic system according to an embodiment is a medical image diagnostic system having a morphological image diagnostic apparatus and a nuclear medicine image diagnostic apparatus, and includes an acquisition unit, a gantry device, and a control unit. The acquisition unit acquires information related to the position of the part of the subject based on the morphological images collected by the morphological image diagnostic apparatus. The gantry device captures a nuclear medicine image of the subject. The control unit controls the gantry device based on information related to the position of the part and imaging conditions for each of the plurality of parts.

FIG. 1 is a diagram for explaining the overall configuration of the medical image diagnostic system according to the first embodiment. FIG. 2 is a block diagram for explaining the overall configuration of the medical image diagnostic system according to the first embodiment. FIG. 3 is a flowchart for explaining a processing flow of the medical image diagnostic system according to the first embodiment. FIG. 4 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the first embodiment. FIG. 5 is a diagram (1) illustrating the setting of imaging conditions according to the medical image diagnostic system according to the second embodiment. FIG. 6A is a diagram (2) illustrating the setting of imaging conditions according to the medical image diagnostic system according to the second embodiment. FIG. 6B is a diagram (3) illustrating the setting of imaging conditions according to the medical image diagnostic system according to the second embodiment. FIG. 6C is a diagram (4) illustrating the setting of imaging conditions according to the medical image diagnostic system according to the second embodiment. FIG. 7 is a view for explaining setting of imaging conditions according to the medical image diagnostic system according to the third embodiment. FIG. 8 is a view for explaining setting of imaging conditions according to the medical image diagnostic system according to the fourth embodiment. FIG. 9 is a diagram for explaining data processing in the medical image diagnostic system according to the fourth embodiment. FIG. 10 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the fifth embodiment. FIG. 11 is a diagram for explaining data processing in the medical image diagnostic system according to the fifth embodiment. FIG. 12 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the sixth embodiment. FIG. 13 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the seventh embodiment.

  Hereinafter, a medical image diagnostic system according to an embodiment will be described in detail with reference to the accompanying drawings.

(First embodiment)
First, the overall configuration of the medical image diagnostic system according to the embodiment will be described with reference to FIGS. 1 and 2. 1 and 2 are diagrams for explaining the overall configuration of the medical image diagnostic system according to the first embodiment.

  As shown in FIG. 1, the medical image diagnostic system according to the first embodiment includes a first gantry device 1, a second gantry device 2, a bed 3, and a console device 4.

  Here, the first gantry device 1 is a gantry device included in the morphological image diagnostic apparatus, for example, and the second gantry device 2 is a gantry apparatus included in the functional image diagnostic device, for example. Examples of the morphological image diagnosis apparatus include an X-ray CT (Computed Tomography) apparatus and an MRI (Magnetic Resonance Imaging) apparatus. Examples of the functional image diagnostic apparatus include, for example, a PET (Positron Emission Tomography) apparatus that is a nuclear medicine imaging apparatus, and a SPECT (Single Photon Emission Computed Tomography) apparatus. Hereinafter, an example in which the first gantry device 1 is a gantry device in an X-ray CT apparatus and the second gantry device 2 is a gantry device in a PET apparatus will be described. At this time, the medical image diagnostic system according to the first embodiment is a PET-CT apparatus.

  The first gantry device 1 detects X-rays transmitted through the subject P, thereby generating X-ray projection data for reconstructing an X-ray CT image and X-ray projection data for generating a scanogram. Device.

  The first gantry device 1 includes the X-ray tube 10, the X-ray detector 15, the data collection unit 16, and the like illustrated in FIG. 2. Here, the X-ray tube 10 is an apparatus that generates an X-ray beam and irradiates the subject P with the generated X-ray beam. The X-ray detector 15 detects X-rays transmitted through the subject P at a position facing the X-ray tube. Specifically, the X-ray detector 15 is a two-dimensional array type detector that detects two-dimensional intensity distribution data (two-dimensional X-ray intensity distribution data) of X-rays transmitted through the subject P. More specifically, in the X-ray detector 15, a plurality of detection element arrays each including a plurality of channels of X-ray detection elements are arranged along the body axis direction of the subject P. The X-ray tube 10 and the X-ray detector 15 are supported inside the first gantry device 1 by a rotating frame (not shown).

  The data collection unit 16 is a DAS (Data Acquisition System), for example, and performs an amplification process, an A / D conversion process, or the like on the two-dimensional X-ray intensity distribution data detected by the X-ray detector 15 to obtain an X Generate line projection data. Then, the data collection unit 16 transmits the X-ray projection data to the console device 4 shown in FIG. The embodiment is not limited to the case where the data collection unit 16 is included in the first gantry device 1, and may be included in the console device 4.

  Returning to FIG. 1, the second gantry device 2 detects a pair of gamma rays emitted from the biological tissue that has taken in the positron emitting nuclide administered to the subject P, thereby generating a gamma ray for reconstructing the PET image. It is a device that generates projection data (gamma ray projection data).

  The second gantry device includes the PET detector 20 shown in FIG. 2, the coincidence counting circuit 12, and the like. The PET detector 20 is a photon counting detector that detects gamma rays emitted from the subject P. Specifically, the PET detector 20 is configured by arranging a plurality of PET detector modules so as to surround the periphery of the subject P in a ring shape.

  For example, the PET detector module is an anger-type detector having a scintillator, a photomultiplier tube (PMT), and a light guide.

  The scintillator has a plurality of two-dimensional arrays of NaI (sodium iodide), BGO (bismuth germanate), and the like that convert incident gamma rays emitted from the subject P into visible light. The photomultiplier tube is a device that multiplies visible light output from the scintillator and converts it into an electrical signal, and a plurality of photomultiplier tubes are arranged densely via a light guide. The light guide is used to transmit visible light output from the scintillator to the photomultiplier tube, and is made of a plastic material having excellent light transmittance.

  The photomultiplier tube includes a photocathode that receives scintillation light and generates photoelectrons, a multistage dynode that provides an electric field that accelerates the generated photoelectrons, and an anode that is an outlet for electrons. Electrons emitted from the photocathode due to the photoelectric effect are accelerated toward the dynode, collide with the surface of the dynode, and knock out a plurality of electrons. By repeating this phenomenon over multiple dynodes, the number of electrons is avalancheally increased, and the number of electrons at the anode reaches about 1 million. In such an example, the gain factor of the photomultiplier tube is 1 million times. In addition, a voltage of 1000 volts or more is usually applied between the dynode and the anode for amplification using the avalanche phenomenon.

  In this manner, the PET detector 20 counts the number of gamma rays emitted from the subject P by converting gamma rays into visible light with a scintillator and converting the converted visible light into electrical signals with a photomultiplier tube. To do.

  The second gantry device 2 includes a coincidence counting circuit 12, for example. The simultaneous coefficient circuit 12 is connected to each of a plurality of photomultiplier tubes included in each module of the PET detector as the plurality of PET detectors 20. Then, the coincidence circuit 12 generates coincidence information for determining the incident direction of the pair of gamma rays emitted from the positron from the output result of the PET detector 20. Specifically, the coincidence counting circuit 12 calculates the position of the center of gravity from the position of the photomultiplier tube that outputs the visible light output from the scintillator to the electrical signal at the same timing and the intensity of the electrical signal, thereby obtaining The incident position (scintillator position) is determined. The coincidence counting circuit 12 calculates the energy value of the incident gamma rays by calculating (integrating and differentiating) the intensity of the electrical signal output from each photomultiplier tube.

  The coincidence counting circuit 12 then selects a combination in which the gamma ray incident timing (time) is within a certain time window width and the energy values are both within a certain energy window width among the output results of the PET detector 20. Search (Coincidence Finding). For example, a time window width of 2 nsec and an energy window width of 350 keV to 550 keV are set as search conditions. Then, the coincidence counting circuit 12 generates coincidence count information (Coincidence List) on the basis of the output result of the searched combination as information obtained by simultaneously counting two annihilation photons. The coincidence counting circuit 12 transmits coincidence counting information to the console device 4 shown in FIG. 1 as gamma ray projection data for PET image reconstruction. A line connecting two detection positions obtained by simultaneously counting two annihilated photons is called a LOR (Line of Response). Further, the coincidence counting information may be generated by the console device 4.

  Returning to FIG. 1, the bed 3 is a bed on which the subject P is placed. The couch 3 sequentially moves to the respective imaging openings of the first gantry device 1 and the second gantry device 2 based on an instruction from an operator of a PET-CT apparatus as a medical image diagnostic system received via the console device 4. Is done.

  That is, the PET-CT apparatus as a medical image diagnostic system first takes an X-ray CT image, which is the first imaging, by moving the bed 3, and then sets the second imaging condition. Set. Thereafter, based on the set imaging conditions, the medical image system performs imaging of a PET image as the second imaging. For example, the first gantry device 1 performs a helical scan in which the imaging region of the subject P is spirally scanned with X-rays by moving the bed 3 while rotating the rotating frame 15 in the main imaging. The console device 4 generates an X-ray CT image based on the obtained data. The generated X-ray CT image may be a 2D image or a 3D image. The first gantry device 1 performs a low-dose helical scan in positioning imaging. The console apparatus 4 generates a helical scan image that is a 3D positioning image based on the obtained data. In addition, the first gantry device 1 moves the bed 3 while irradiating X-rays from the X-ray tube while fixing the rotating frame in positioning imaging, so that the whole body of the subject P is moved along the body axis direction. Scanning may be performed, and the console device 4 may generate an X-ray CT image (scan image) that is a 2D positioning image.

  The second gantry device 2 generates a PET image by moving the bed 3 so that the imaging part of the subject P is inserted into the imaging port of the second gantry device 2.

  The console device 4 is a device that receives an instruction from an operator and controls imaging processing in the medical image diagnostic apparatus.

  As shown in FIG. 2, the console device 4 includes, for example, a storage circuit 30 and a processing circuit 5. The processing circuit 5 includes, for example, an image generation function 31, a setting function 32, a specific function 33, a control function 34, a reception function 35, an input device 36, and a display 37. Examples of the image generation function 31 include a first generation function 11 and a second generation function 12.

  Here, the setting function 32, the specific function 33, the reception function 35, the first generation function 11, the second generation function 12, and the image generation function 31 shown in FIG. 2 are respectively a setting unit, a specific unit, a reception unit, and a first generation. Part, second generation unit, and image generation unit.

  In the embodiment in FIG. 2, each processing function performed by the image generation function 31 (first generation function 11, second generation function 12), setting function 32, specific function 33, control function 34, and reception function 35 is a computer. Is stored in the storage circuit 30 in the form of an executable program. The processing circuit 5 is a processor that realizes a function corresponding to each program by reading the program from the storage circuit 30 and executing the program. In other words, the processing circuit 5 in a state where each program is read has the functions shown in the processing circuit 5 of FIG. In FIG. 2, a single processing circuit 5 uses an image generation function 31 (first generation function 11, second generation function 12), a setting function 32, a specific function 33, a control function 34, and a reception unit 35. Although the processing function to be performed has been described as being realized, the processing circuit 5 may be configured by combining a plurality of independent processors, and the function may be realized by each processor executing a program.

  In other words, each function described above may be configured as a program, and one processing circuit may execute each program, or a specific function may be implemented in a dedicated independent program execution circuit. May be.

  The term “processor” used in the above description refers to, for example, a CPU (central processing unit), a GPU (Graphical processing unit), an application specific integrated circuit (ASIC), a programmable logic device (for example), or the like. It means a circuit such as a simple programmable logic device (SPLD), a complex programmable logic device (Complex Programmable Logic Device), and a field programmable gate array (FPGA). That. The processor implements a function by reading and executing a program stored in the storage circuit 30. Instead of storing the program in the storage circuit 30, the program may be directly incorporated into the processor circuit. In this case, the processor realizes the function by reading and executing the program incorporated in the circuit.

  Furthermore, the storage circuit 30 stores the X-ray projection data transmitted from the first gantry device 1. Specifically, the storage circuit 30 stores X-ray projection data for generating a scanogram and X-ray projection data for reconstructing an X-ray CT image by the first generation function 11.

  The processing circuit 5 generates a scanogram from the X-ray projection data for generating the scanogram stored in the storage circuit 30 by the image generation function 31. The processing circuit 5 uses the first generation function 11 to back-project the reconstruction X-ray projection data stored in the storage circuit 30 by, for example, the FBP (Filtered Back Projection) method, thereby converting the X-ray CT image. Reconfigure.

  That is, the processing circuit 5 generates a morphological image by using the first generation function 11 to generate a scanogram for making an imaging plan in the whole body examination using the PET-CT apparatus. Then, the processing circuit 5 uses the first generation function 11 to calculate from the X-ray projection data based on the imaging conditions (for example, slice width) determined by the imaging plan in the whole body examination using the PET-CT apparatus. A plurality of X-ray CT images obtained by photographing a plurality of cross sections orthogonal to the body axis direction of the subject P are reconstructed.

  For example, the processing circuit 5 uses the first generation function 11 to reconstruct volume data or two-dimensional tomographic image data based on the projection data stored in the storage circuit 30. Volume data and two-dimensional tomographic image data are collectively referred to as “image”. In order to display image data and an operation screen, a display unit (not shown) is provided in the console device 4. Further, the processing circuit 5 receives an operator's instruction through the input device 36 by the reception function 35. The input device 36 is composed of, for example, a keyboard and a mouse.

  The processing circuit 5 performs image processing such as pattern recognition from a morphological image (helical scan image) obtained by performing an X-ray CT helical scan on the subject by the anatomical landmark detection function included in the specifying function 33. Thus, a plurality of anatomical feature points are extracted based on the morphological features and the like. The position data of each anatomical feature point and the identification code of each anatomical feature are held in the storage circuit 30. In addition, the processing circuit 5 uses the anatomical landmark detection function included in the specifying function 33 to perform image processing such as pattern recognition on the basis of anatomical features from image data acquired by actual imaging. It is also possible to extract feature points.

  That is, the processing circuit 5 uses the specifying function 33 to specify the position of the feature point of the subject P from the morphological image, and specifies the site of the subject P based on the specified position of the feature point. Further, the processing circuit 5 specifies the position of the feature point of the subject P from the morphological image by the specifying function 33 not only in the positioning shooting but also in the main shooting, and based on the position of the specified feature point. Thus, the site of the subject P may be specified.

  Note that the method of specifying the part of the subject P by the processing circuit 5 using the specifying function 33 is not limited to the method of specifying based on the position of the feature point specified by the anatomical landmark detection function as described above. For example, the processing circuit 5 may specify the region of the above-described subject P by using a region recognition method other than the anatomical landmark detection.

  Further, the processing circuit 5 may receive an operator's instruction from an input / output device (not shown) by the reception function 35. For example, in the second imaging performed by the second gantry device 2 by the reception function 35, the processing circuit 5 inputs an imaging condition (imaging condition for each part) according to the part of the subject to be input / output device (not shown). Accept from. For example, the processing circuit 5 sets the imaging conditions corresponding to the part of the second imaging for the part of the subject specified by the specifying function 33 by the setting function 32. For example, the processing circuit 5 uses the setting function 33 to set the imaging condition corresponding to the part of the second imaging based on the input of the imaging condition received by the reception function 35.

  The processing circuit 5 controls processing of the entire medical image diagnostic apparatus by the control function 34. Specifically, the processing circuit 5 controls imaging by the medical image diagnostic apparatus by controlling the first gantry device 1 and the second gantry device 2 by the control function 34. Further, the processing circuit 5 controls the execution of the second generation function 12 by using the data stored in the storage circuit 30 by the control function 34. Further, the processing circuit 5 controls the execution of the scanogram generation function and the second generation function 12 using the data stored in the storage circuit 30 by the control function 34. Further, the processing circuit 5 causes the control function 34 to display a GUI (Graphical User Interface) for an operator to input an instruction, a scanogram, an X-ray CT image, and a PET image with an input / output device (not shown). To control. Further, the processing circuit 5 controls the processing by which the second gantry device 2 generates a functional image based on the second imaging according to the imaging condition set by the processing circuit 5 by the setting function 32 by the control function 34.

  The storage circuit 30 stores not only the projection data transmitted from the first gantry device 1 but also the gamma ray projection data transmitted from the coincidence circuit included in the second gantry device 2. At this time, the processing circuit 5 reconstructs the PET image by the successive approximation method from the gamma ray projection data stored in the storage circuit 30 by the second generation function 12.

  Hereinafter, the successive approximation method executed by the second generation function 12 will be described. As the successive approximation method, there are an MLEM (Maximum Likelihood Expectation Maximization) method and an OSEM (Ordered Subset MLEM) method in which the convergence time is significantly shortened by improving the algorithm of the MLEM method.

  In the MLEM method, a PET image is reconstructed from an actually collected gamma ray projection data as an initial image by back projection processing such as the FBP method. The estimated projection data of the first iteration is generated by projecting the initial image, and the reconstructed image of the first iteration is reconstructed by backprojecting the estimated projection data of the first iteration. The Then, the reconstructed image of the first iteration is projected to generate estimated projection data of the second iteration, and the estimated projection data of the second iteration is back-projected to regenerate the second iteration. The composition image is reconstructed. Such processing is repeated for the number of iterations of successive approximation. In the following, the number of repeated operations is referred to as an iteration number.

  As a result, estimated projection data in which the ratio with the actually collected projection data is converged to approximately “1” is generated. A reconstructed image obtained by back-projecting the converged estimated projection data is a PET image representing the most probabilistic most probable positron emission nuclide accumulation distribution.

  The OSEM method is a method of correcting an image by dividing gamma ray projection data into several subsets and performing the above-described successive approximation for each subset. That is, the OSEM method in which the division number (subset number) is “1” is the MLEM method.

  Here, the total number of operations in the second generation function 12 depends on the number of iterations when the MLEM method is executed. The total number of operations in the second generation function 12 depends on the number obtained by multiplying the number of subsets by the number of iterations when executing the OSEM method.

  Hereinafter, a case where the processing circuit 5 reconstructs a PET image by the OSEM method in the second generation function 12 will be described. However, the embodiment is applicable even when the processing circuit 5 reconstructs a PET image by the MLEM method in the second generation function 12.

  The processing circuit 5 included in the console device 4 according to the medical image diagnostic system according to the first embodiment includes a first generation function 11, a specifying function 33, a setting function 22, and a second generation function 12. The processing circuit 5 uses the first generation function 11 to generate a morphological image based on the first imaging for the subject. The processing circuit 5 specifies the position of the feature point of the subject from the morphological image by the specifying function 33, and specifies the site of the subject based on the specified position of the feature point. The processing circuit 5 sets the imaging condition (imaging condition for each of a plurality of parts) of the second imaging for the part specified by the specifying function 33 by the setting function 22. The processing circuit 5 generates a functional image (nuclear medicine image) based on the second imaging performed in accordance with the imaging condition corresponding to the region by the second generation function.

  In other words, the medical image diagnosis system according to the first embodiment includes, for example, a medical image diagnosis including a morphological image diagnosis apparatus (for example, the first gantry apparatus 1) and a nuclear medicine image diagnosis apparatus (for example, the second gantry apparatus). System. The medical image diagnostic system includes a processing circuit 5 and a gantry device (for example, the second gantry device 2). The processing circuit 5 acquires information related to the part of the subject P based on the morphological image collected by the morphological image diagnostic apparatus by an acquisition unit (not shown). The gantry device captures a nuclear medicine image of the subject. The processing circuit 5 controls the gantry device based on the acquired information related to the part of the subject P and the imaging conditions for each of the plurality of parts.

  Further, the processing circuit 5 may further include a reception function 35. In such a case, the processing circuit 5 receives an input of imaging conditions corresponding to the part by the reception function 35. Further, the processing circuit 5 sets the imaging condition corresponding to the part of the second imaging based on the input of the imaging condition received by the reception function 35 by the setting function 22.

  These points will be described with reference to FIGS. FIG. 3 is a flowchart for explaining the flow of processing of the medical image diagnostic system according to the first embodiment. The processing circuit 5 implements various functions by calling and executing predetermined programs corresponding to the various functions from the storage circuit 30. FIG. 4 is a diagram illustrating setting of imaging conditions according to the medical image diagnostic system according to the first embodiment. Hereinafter, each step of the flowchart of FIG. 3 will be described with reference to FIG. 4 as appropriate.

  The processing circuit 5 receives an input of imaging conditions (imaging conditions for each of a plurality of parts) according to the part of the subject in the second imaging by the reception function 35. Here, the second imaging is, for example, PET imaging using the second gantry device 2. The processing circuit 5 receives an input of parameter setting from the operator by the reception function 35 (step S101). The parameters referred to here are, for example, settings of a specific part, its collection time, and collection time for whole body imaging (more specifically, imaging of parts other than the specific part). That is, the processing circuit 5 receives an input of an imaging time or an imaging speed in the imaging range as an imaging condition (imaging condition for each of a plurality of parts) according to the part of the subject by the reception function 35. The processing circuit 5 accepts an input of the collection time “5 minutes per position” from the operator as an imaging condition corresponding to the part, for example, for the part “head” by the accepting function 35. Further, the processing circuit 5 accepts an input of the collection time “2 minutes per position” as an imaging condition corresponding to the part “whole body (part other than the head)” by the reception function 35. Here, “one position” refers to a range in which imaging is performed in one step, for example, in the case where imaging is performed by the step-and-shoot method using a PET apparatus in the second imaging.

  As another example, the processing circuit 5 may receive an input of the collection time required for imaging the entire predetermined part, instead of the collection time per position, from the operator by the reception function 35. . For example, the processing circuit 5 accepts an input of the collection time “15 minutes in total” as an imaging condition corresponding to the part to the part “head” by the reception function 35, and the part “whole body (other than the head part) ) ”May be received as an imaging condition corresponding to the part.

  When the processing circuit 5 receives an input of parameter setting from the operator by the reception function 35, the first gantry device 1 performs first imaging (step S102). Here, the first imaging is X-ray CT imaging using, for example, an X-ray CT apparatus. For example, the first gantry device 1 performs X-ray CT imaging by low-dose helical scan.

  The processing circuit 5 uses the first generation function 11 to generate a morphological image based on the first imaging for the subject.

  The processing circuit 5 uses the specifying function 33 to specify the position of the feature point of the subject from the generated morphological image. That is, the processing circuit 5 extracts a predetermined part (step S103). For example, the processing software constituting the processing circuit 5 automatically extracts a predetermined part from the photographed low-dose helical scan image.

  Subsequently, the processing circuit 5 uses the specifying function 33 to specify a predetermined part of the subject based on the position of the specified feature point. Alternatively, the processing circuit 5 uses the specifying function 33 to specify a plurality of parts of the subject based on the position of the specified feature point. That is, the processing circuit 5 specifies the position of a predetermined part (or a plurality of parts) by the specifying function 33 (step S104).

  In FIG. 4, the part specified by the specifying function 33 of the processing circuit 5 in this way is displayed superimposed on the imaging range of the second imaging. In this example, the processing circuit 5 uses the specifying function 33 to specify the region “head 50A” as the imaging range 54A. The processing circuit 5 identifies the region “whole body (region other than the head)” as the imaging range 54B by the identifying function 33.

  The processing circuit 5 uses the setting function 32 to set the imaging conditions corresponding to the part of the second imaging for the part specified by the specifying function 33. Alternatively, the processing circuit 5 uses the setting function 32 to set imaging conditions corresponding to each of the plurality of parts for the second imaging for each of the specified parts. For example, the processing circuit 5 uses the setting function 32 to set the imaging condition corresponding to the part of the second imaging based on the input of the imaging condition received by the reception function 35 (step S105). For example, the processing circuit 5 sets the collection time (shooting time or shooting speed) by the setting function 32.

  For example, the processing circuit 5 sets the imaging condition “5 minutes per position” corresponding to the part to the imaging range 54 </ b> A specified as the part “head” by the setting function 32. Further, the processing circuit 5 sets the imaging condition “2 minutes per position” corresponding to the part to the imaging range 54B specified as the part “whole body (part other than the head)” by the setting function 32. .

  In addition, the processing circuit 5 may set the collection time required for imaging the entire predetermined portion, not the collection time per position, by the setting function 32. For example, the processing circuit 5 sets the imaging condition “total 15 minutes” corresponding to the part to the imaging range 54A specified as the part “head” by the setting function 32, and sets the part “whole body (other than the head). The imaging condition “20 minutes in total” may be set for the imaging range 54B specified as “part)”.

  Further, the processing circuit 5 sets other parameters as required by the setting function 32.

  Each of the areas 51 and 52 indicates a first position imaging area and a second position imaging area in the imaging of the part “head” in the second imaging. As described above, the second gantry device 2 performs the second imaging while overlapping the imaging locations for each position.

  When the processing circuit 5 sets the shooting conditions such as the acquisition time and other parameters, the processing circuit 5 displays the set shooting conditions and the like on a display device such as a display (step S106). For example, the processing circuit 5 has the imaging condition “5 minutes per position” set for the part “head” on the display, and the part “whole body (part other than the head)” is imaged. A message indicating that the range “2 minutes per position” is set is displayed. Further, for example, the processing circuit 5 specifies, on the morphological image generated by the first imaging on the display, the imaging range 54A specified as the part “head” and the part “whole body (part other than the head)”. The captured imaging range 54B is displayed in an overlapping manner. Further, the processing circuit 5 has the imaging condition “5 minutes per position” for the part “head” in the morphological image on the display, and the part “whole body (part other than the head)” ”Is also displayed together with a message indicating that the photographing range“ 2 minutes per position ”is set.

  The processing circuit 5 receives an input from the operator through the input device 36. Based on the input from the operator, the processing circuit 5 determines whether or not an input for approving the photographing condition has been received by the reception function 35 (step S107). If the operator does not approve the shooting condition, the processing circuit 5 determines that the input for approving the shooting condition is not received by the reception function 35 (No in step S107), and repeats the same processing as in step S101 to perform the operation. Accepts re-input of parameter settings from the user. After that, based on the parameters re-input by the operator, the processing circuit 5 returns to step S105 and sets the shooting conditions again by the setting function 32.

  When the operator approves the imaging condition, the processing circuit 5 determines that the input for approving the imaging condition is received by the reception function 35 (Yes in step S107), and the processing function of the second gantry device 2 is set by the processing circuit 5 The second imaging for generating the functional image is performed in accordance with the imaging condition corresponding to the region set by 32. Alternatively, the second gantry device 2 performs second imaging for generating a functional image in accordance with imaging conditions corresponding to each of the plurality of parts set by the processing function 5 using the setting function 32 (step S108).

  When the second imaging is completed, the processing circuit 5 generates a functional image based on the second imaging performed in accordance with the imaging condition corresponding to the part by the second generation function 12 (step S109), or a plurality of functions A functional image is generated based on the second imaging performed according to the imaging condition corresponding to each part, and the process ends.

  As described above, in the first embodiment, the processing circuit 5 uses the specifying function 33 to specify the position of the feature point of the subject from the morphological image, and based on the position of the specified feature point, the part of the subject Is identified. Further, the processing circuit 5 sets the imaging condition corresponding to the part of the second imaging for the specified part by the setting function 32. In addition, the processing circuit 5 generates a functional image based on the second imaging performed according to the imaging condition corresponding to the part by the second generation function 12. In particular, an input of an imaging time or an imaging speed is accepted as an imaging condition corresponding to the part.

  Thereby, according to the medical image diagnostic system which concerns on 1st Embodiment, an operator's burden can be eased. In particular, it is possible to set different imaging speeds for parts that require high-accuracy imaging for diagnosis and parts that do not require high-accuracy imaging. However, according to the medical image diagnostic system according to the first embodiment, the user does not have to manually set the imaging range. Therefore, it is possible to acquire an accurate image while reducing the burden on the operator.

(Second Embodiment)
In 1st Embodiment, the case where the input of imaging time or imaging speed was received as imaging conditions according to the site | part was demonstrated. In the second embodiment, the size of FOV (Field Of View) is set as the imaging condition corresponding to the part as the imaging condition corresponding to the part.
As a result, it is not necessary to set an unnecessarily large FOV size for the part, and errors due to events (background scattered components) related to an area unrelated to imaging can be reduced. The image quality of functional images can be improved.

  The processing circuit 5 included in the medical image diagnostic system according to the second embodiment sets the size of the FOV by the setting function 32.

  Processing performed by the medical image diagnostic system according to the second embodiment will be described with reference to FIGS. 3, 5, 6A, 6B, and 6C. 5, 6A, 6B, and 6C are diagrams for describing setting of imaging conditions according to the medical image diagnostic system according to the second embodiment.

  In the second embodiment, similarly to the first embodiment, the processing described in the flowchart of FIG. 3 is performed, but the processing in step S105 is different from that in the first embodiment. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  As shown in FIG. 5, in the second embodiment, by performing the same processing as in the first embodiment, in step S <b> 104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 5, the processing circuit 5 specifies the region “head” as the imaging range 64 </ b> A by the specifying function 33. The processing circuit 5 uses the specifying function 33 to specify the region “shoulder to lower abdomen” as the imaging range 64B. The processing circuit 5 specifies the region “lower limb” as the imaging range 64 </ b> C by the specifying function 33.

  In the second embodiment, the processing circuit 5 sets the size of the FOV by the setting function 32 in step S105. FIG. 6A is an axial cross-sectional image for the region “head”, and the boundary 71A corresponds to the body surface of the subject. Similarly, FIG. 6B is an axial cross-sectional image with respect to the site “shoulder to lower abdomen”, and the boundary 71B corresponds to the body surface of the subject. Similarly, FIG. 6C is an axial cross-sectional image of the region “lower limb”, and the boundary 71C corresponds to the body surface of the subject.

  Here, the processing circuit 5 sets the area 71 </ b> A of FIG. 6A as an FOV for the imaging range 64 </ b> A specified as the part “head” by the setting function 32. Specifically, the processing circuit 5 sets an area including the entire body surface 70A of the subject as the area 71A by the setting function 32. Similarly, the processing circuit 5 sets the region 71B of FIG. 6B as the FOV for the imaging range 64B specified as the region “shoulder to lower abdomen” by the setting function 32. The processing circuit 5 sets the region 71C in FIG. 6C as the FOV for the imaging range 64C specified as the region “lower limb” by the setting function 32. The processing circuit 5 performs the same processing as in the first embodiment based on the shooting conditions set in this way.

  Thus, in the second embodiment, the processing circuit 5 sets the size of the FOV by the setting function 32. The reason is as follows. In PET, the detector detects a pair of γ-ray pairs generated in the pair annihilation, but if the FOV is unnecessarily large for the site, a signal of γ-rays generated at a place unrelated to the subject. The detector detects (background scattered component). As a result, noise increases and the quality of the functional image obtained decreases. For this reason, it is desirable that the size of the FOV is not unnecessarily large compared to the site of the subject. In the second embodiment, since the processing circuit 5 automatically sets the size of the FOV by the setting function 32, it is not necessary to set an unnecessarily large size of the FOV for the part. As a result, an error due to an event relating to an area unrelated to imaging can be reduced, and the quality of the functional image can be improved. Although it is possible for the operator to perform this operation manually, if the operator manually performs an operation for setting the size of the FOV, the burden on the operator is large. In the medical image diagnostic system according to the second embodiment, maintaining the image quality of the functional image can be compatible with reducing the burden on the operator.

(Third embodiment)
In the third embodiment, an input of the size of the overlapping area for each imaging is set as an imaging condition corresponding to the part. As a result, it is possible to simultaneously reduce the shooting time while maintaining the image quality (S / N ratio) of the functional image and to reduce the burden on the operator.

  In the third embodiment, the processing circuit 5 inputs the size of the overlapping area of each imaging in the case where the reception function 35 divides the second imaging into a plurality of imagings for a predetermined part. Is accepted as an imaging condition corresponding to the part. The processing circuit 5 sets the imaging condition corresponding to the part of the second imaging based on the received imaging condition input by the setting function 32.

  Processing performed by the medical image diagnostic system according to the third embodiment will be described with reference to FIGS. 3 and 7. FIG. 7 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the third embodiment.

  In the third embodiment, similarly to the first embodiment, the processing described in the flowchart of FIG. 3 is performed, but the processing in steps S101 and S105 is different from that in the first embodiment. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  As described above, the second gantry device 2 normally performs the second imaging while overlapping the imaging locations for each position. The processing circuit 5 accepts an input of the size of the overlap (overlapping) area as an imaging condition. Specifically, in step S101, the processing circuit 5 uses the reception function 35 to perform second imaging on a predetermined part as imaging conditions (imaging conditions for each of a plurality of parts) according to the part of the subject. In the case of performing the imaging separately for a plurality of times, an input of the size of the overlapping area of each time of imaging is accepted as an imaging condition corresponding to the part. For example, the processing circuit 5 receives an input of the overlap region size “50%” for the region “head” as the imaging condition corresponding to the region of the subject by the reception function 35. Further, the processing circuit 5 receives an input of the overlap region size “30%” for the region “lower limb” as the imaging condition corresponding to the region of the subject by the reception function 35. Further, the processing circuit 5 accepts an input of the size of the overlapping region “40%” for the region “other” as the imaging condition corresponding to the region of the subject by the reception function 35.

  As shown in FIG. 7, in the third embodiment, by performing the same processing as in the first embodiment, in step S <b> 104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 7, the processing circuit 5 specifies the region “head” as the imaging range 82 </ b> A by the specifying function 33. The processing circuit 5 identifies the region “lower limb” as the imaging range 82 </ b> C by the identifying function 33. The processing circuit 5 identifies the part “others” as the imaging range 82 </ b> B by the identifying function 33.

  In the third embodiment, in step S <b> 105, the processing circuit 5 sets the size of the overlapping area for each shooting using the setting function 32.

  The processing circuit 5 sets “50%” as the size of the overlapping region of the imaging in the imaging range 82 </ b> A specified as the part “head” by the setting function 32. Similarly, the processing circuit 5 sets “30%” as the size of the imaging overlapping area in the imaging range 82 </ b> B specified as the region “lower limb” by the setting function 32. Similarly, the processing circuit 5 sets “40%” as the size of the overlapping region of the imaging in the imaging range 82 </ b> C specified as the part “other” by the setting function 32. The processing circuit 5 performs the same processing as in the first embodiment based on the shooting conditions set in this way.

  In this way, in the third embodiment, the processing circuit 5 sets the size of the overlapping area for each shooting by the setting function 32. The reason is as follows. In PET, when imaging by the step-and-shoot method, the detection efficiency is reduced because γ-rays are detected at the ends of the detector at both ends of each position compared to the vicinity of the center of each position. . Therefore, in order to compensate for the effect, data is compensated by providing an overlap area for each photographing. As the size of the overlapping area is larger, the accuracy (S / N ratio) of the obtained data is increased. However, as the overlapping area is larger, the entire imaging time is increased. Therefore, since the accuracy of the finally required data varies from part to part, setting the size of the overlapping area for each part shortens the entire imaging time, while reducing the data of the necessary part. Accuracy can be maintained. Although this operation can be manually performed by the operator, if the operator manually performs the operation of setting the size of the overlapping area, the burden on the operator is large. According to the medical image diagnostic system according to the third embodiment, it is possible to reduce both the imaging time and the burden on the operator while maintaining the image quality (S / N ratio) of the functional image. Can do.

(Fourth embodiment)
In the fourth embodiment, the processing circuit 5 sets imaging conditions for synchronous imaging such as respiratory synchronous imaging and electrocardiographic synchronous imaging.

  In the fourth embodiment, the processing circuit 5 accepts input of imaging conditions for synchronous imaging as imaging conditions (imaging conditions for each of a plurality of parts) according to the part by the reception function 35. The processing circuit 5 sets the imaging condition corresponding to the part of the second imaging based on the received imaging condition input by the setting function 32.

  Processing performed by the medical image diagnostic system according to the fourth embodiment will be described with reference to FIGS. 3, 8, and 9. FIG. 8 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the fourth embodiment. FIG. 9 is a diagram for explaining data processing in the medical image diagnostic system according to the fourth embodiment.

  In the fourth embodiment, the processing described in the flowchart of FIG. 3 is performed as in the first embodiment. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  In step S <b> 101, the processing circuit 5 uses the reception function 35 to accept input of imaging conditions for synchronous imaging as imaging conditions (imaging conditions for each of a plurality of sites) corresponding to the site. The processing circuit 5 uses the reception function 35 to indicate “respiratory synchronization” and “respiratory synchronization parameters” for the region “chest 90” shown in FIG. 8 as imaging conditions according to the region of the subject. "Is accepted. As another example, the processing circuit 5 uses the reception function 35 to indicate that “electrocardiographic synchronization is performed” and “parameters related to electrocardiographic synchronization” for the region “heart” as imaging conditions corresponding to the region of the subject. "Is accepted. As another example, the processing circuit 5 performs “synchronous imaging combining respiratory synchronization and electrocardiographic synchronization” with respect to a predetermined region as an imaging condition corresponding to the region of the subject by the reception function 35. ”And“ predetermined parameters ”are received. In addition, the processing circuit 5 uses the reception function 35 to set a predetermined condition for the region “head”, the region “others”, and the like shown in FIG. 8 as imaging conditions corresponding to the region of the subject. Accept input.

  Synchronous imaging refers to imaging in association with an event that continues to be repeated at a predetermined interval, for example, respiratory synchronization in which imaging is performed in association with a respiratory phase, and imaging in association with an electrocardiographic phase. This is ECG-synchronized shooting. When performing respiratory synchronization imaging, the second gantry device 2 performs imaging at a plurality of times in association with the respiratory phase, and collects data at each of the plurality of times. For example, the processing circuit 5 collects the data of each of the plurality of times associated with the respiratory phase for each respiratory phase by using the second generation function, thereby generating a functional image for each respiratory phase (diastolic phase, systolic phase, etc.). Generate. Examples of parameters relating to respiratory synchronization include the number of times of performing respiratory synchronization imaging, the imaging start time, the imaging end time, the imaging time, and the imaging interval. In addition, when performing electrocardiogram synchronous imaging, the second gantry device 2 performs imaging at a plurality of times in association with the electrocardiographic phase, and collects data at each of the plurality of times. The processing circuit 5 uses the second generation function to, for example, summarize the data of each of the plurality of times associated with the electrocardiographic phase for each electrocardiographic phase, thereby for each electrocardiographic phase (systole, diastole). Generate a functional image of Examples of parameters relating to electrocardiographic synchronization include the number of times of performing electrocardiographic synchronization imaging, imaging start time, imaging end time, imaging time, imaging interval, and the like.

  As shown in FIG. 8, in the fourth embodiment, by performing the same processing as in the first embodiment, in step S <b> 104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 8, the processing circuit 5 specifies the region “head” as the imaging range 91 </ b> A by the specifying function 33. The processing circuit 5 uses the specifying function 33 to specify the region “chest” as the imaging range 91B. The processing circuit 5 identifies the part “others” as the imaging range 82 </ b> B by the identifying function 33.

  In the fourth embodiment, in step S105, the processing circuit 5 uses the setting function 32 to set synchronous imaging conditions as imaging conditions (imaging conditions for each of a plurality of parts) according to the part. The processing circuit 5 uses the setting function 32 to set “perform respiratory synchronized imaging” and “parameters related to respiratory synchronized imaging” as imaging conditions in the imaging range 91B specified as the region “chest”. The processing circuit 5 uses the setting function 32 to perform the same settings as those in the first embodiment for parts other than the part “chest”.

  In step S <b> 108, the second gantry device 2 performs the second imaging in accordance with the imaging conditions corresponding to the part set by the processing circuit 5 using the setting function 32.

  For example, FIG. 9 illustrates this situation. The second gantry device 2 performs imaging at a time corresponding to the first respiratory phase, and collects data 110A and data 111A. The second gantry device 2 performs imaging at a time corresponding to the second respiratory phase, and collects data 110B and data 111B. The second gantry device 2 performs imaging at a time corresponding to the third respiratory phase, and collects data 110C and data 111C.

  Here, the data 110A, the data 110B, and the data 110C are data related to the region “chest” that is the target of the synchronous imaging. The data data 111A, data 111B, and data 111C are data related to a part other than the part “chest”.

  In step S109, when the second imaging is finished, the processing circuit 5 causes the second generation function 12 to generate a functional image based on the second imaging performed according to the imaging condition corresponding to the part. Specifically, the processing circuit 5 uses the second generation function 12 to integrate data for each phase and generate an image for each phase with respect to a portion where synchronous imaging is performed. On the other hand, the processing circuit 5 uses the second generation function 12 to integrate all phase data for a part that is not subjected to synchronous imaging, and generates one image based on the integrated data.

  Specifically, for the region “chest”, the processing circuit 5 uses the second generation function 12 to generate data 110A corresponding to the first respiratory phase, data 110B corresponding to the second respiratory phase, and third respiratory The data 110C corresponding to the phase is integrated to generate data for each respiratory phase, and based on that, an image for each respiratory phase is generated. On the other hand, for the part other than the part “chest”, the processing circuit 5 uses the second generation function 12 to integrate the data 111A, the data 111B, and the data 111C to generate one data, and based on the data, Is generated.

  As described above, in the fourth embodiment, the processing circuit 5 sets the imaging condition for the synchronous imaging as the imaging condition corresponding to the part by the setting function 32. The reason is as follows. Since parts such as the chest and heart have movement, it is desirable to perform special processing such as synchronous imaging unlike other parts. However, it is troublesome for the operator to manually set such parameters. When the processing circuit 5 sets the photographing conditions for synchronous photographing, the medical image diagnostic system according to the fourth embodiment can reduce the burden on the operator.

(Fifth embodiment)
In the fifth embodiment, the processing circuit 5 sets shooting conditions for dynamic shooting.

  In the fifth embodiment, the processing circuit 5 accepts input of imaging conditions for dynamic imaging as imaging conditions (imaging conditions for each of a plurality of parts) according to the part by the reception function 35. The processing circuit 5 sets the imaging condition corresponding to the part of the second imaging based on the received imaging condition input by the setting function 32.

  Processing performed by the medical image diagnostic system according to the fifth embodiment will be described with reference to FIGS. 3, 10, and 11. FIG. 10 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the fifth embodiment. FIG. 11 is a diagram for explaining data processing in the medical image diagnostic system according to the fifth embodiment.

  In the fifth embodiment, similarly to the first embodiment, the processing described in the flowchart of FIG. 3 is performed. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  In step S <b> 101, the processing circuit 5 accepts input of imaging conditions for dynamic imaging as imaging conditions (imaging conditions for each of a plurality of parts) according to the part by the reception function 35. The processing circuit 5 uses the reception function 35 to indicate “dynamic imaging” and “dynamic parameters” for the region “heart” shown in FIG. 10 as the imaging conditions according to the region of the subject. Accept input. In addition, the processing circuit 5 uses the reception function 35 to set a predetermined condition for the region “head”, the region “others”, and the like shown in FIG. 8 as imaging conditions corresponding to the region of the subject. Accept input.

  Here, the dynamic imaging is imaging in which temporal changes in a predetermined part can be seen, for example, by imaging in time series (time phase). Both dynamic imaging and synchronous imaging are common in that a change in time of a predetermined part is observed. Synchronous imaging is imaging that focuses on motion at a predetermined phase in periodically repeated movements such as breathing and heartbeat, whereas dynamic imaging is imaging that focuses on transient characteristics with respect to, for example, contrast medium injection. For example, it is performed for the purpose of observing vascular dynamics in a lesion. For example, in normal imaging, a contrast medium is injected at a predetermined injection speed, and imaging is started when the contrast medium concentration in blood reaches equilibrium. As a result, imaging in the equilibrium phase can be performed. On the other hand, in dynamic imaging, for example, the contrast agent injection speed is increased compared to normal imaging, contrast medium injection is performed in a short period of time, and imaging is performed before the contrast agent concentration in the blood reaches equilibrium. Characteristic (arterial layer) can be observed.

  Examples of parameters related to dynamic shooting include the number of shootings for dynamic shooting, shooting start time, shooting end time, shooting time, shooting interval, and the like.

  As shown in FIG. 10, in the fifth embodiment, by performing the same processing as in the first embodiment, in step S <b> 104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 10, the processing circuit 5 specifies the region “head” as the imaging range 120 </ b> A by the specifying function 33. The processing circuit 5 uses the specifying function 33 to specify the region “heart” as the imaging range 120B. The processing circuit 5 specifies the region “lower limb” as the imaging range 120 </ b> C by the specifying function 33.

  In the fifth embodiment, in step S105, the processing circuit 5 uses the setting function 32 to set imaging conditions for dynamic imaging as imaging conditions (imaging conditions for each of a plurality of sites) according to the site. The processing circuit 5 uses the setting function 32 to set “dynamic imaging” and “parameters related to dynamic imaging” as imaging conditions in the imaging range 120B specified as the region “heart”. The processing circuit 5 uses the setting function 32 to perform the same setting as in the first embodiment for the parts other than the part “heart”.

  In step S <b> 108, the second gantry device 2 performs the second imaging in accordance with the imaging conditions corresponding to the part set by the processing circuit 5 using the setting function 32.

  For example, this situation is shown in FIG. The second gantry device 2 performs imaging at a time corresponding to the first time phase and collects data 130A and data 131A. The second gantry device 2 performs imaging at a time corresponding to the second time phase, and collects data 130B and data 131B. The second gantry device 2 captures data 130 </ b> C and data 131 </ b> C by photographing at a time corresponding to the third time phase.

  Here, the data 130A, the data 130B, and the data 130C are data related to the region “heart” that is a target of dynamic imaging. The data data 131A, data 131B, and data 131C are data related to a part other than the part “heart”.

  In step S109, when the second imaging is finished, the processing circuit 5 causes the second generation function 12 to generate a functional image based on the second imaging performed according to the imaging condition corresponding to the part. Specifically, the processing circuit 5 uses the second generation function 12 to integrate data regarding the part to be subjected to dynamic imaging, and generates a time-series image based on the data. On the other hand, the processing circuit 5 uses the second generation function 12 to integrate all time phase data and generate one image based on the data for a portion where dynamic imaging is not performed.

  Specifically, for the region “heart”, the processing circuit 5 causes the second generation function 12 to use the data 130A corresponding to the first time phase, the data 130B corresponding to the second time phase, and the third time. The data 130C corresponding to the phases are integrated to generate data for each time phase, and a time-series image is generated based on the data. On the other hand, for the part other than the part “heart”, the processing circuit 5 uses the second generation function 12 to integrate the data 131A, the data 131B, and the data 131C to generate one data, and based on the data, Is generated.

  Thus, in the fifth embodiment, the processing circuit 5 sets the imaging conditions for dynamic imaging as the imaging conditions corresponding to the part by the setting function 32. The part for performing dynamic imaging requires parameter settings different from the part for performing normal imaging, but it is troublesome for the operator to manually set such parameters. By setting the imaging conditions for dynamic imaging by the processing circuit 5, according to the medical image diagnostic system according to the fifth embodiment, the burden on the operator can be reduced.

(Sixth embodiment)
In the embodiments so far, the case has been described in which the second gantry device 2 performs imaging by the step-and-shoot method, but the embodiments are not limited thereto. In the sixth embodiment, the second imaging is continuous imaging performed by continuously moving the imaging region of the subject.

  Here, the continuous imaging (Continuous imaging) method is an imaging method in which the imaging region of the subject is continuously moved, instead of imaging by the step-and-shoot method. In the step-and-shoot method, since the imaging region is changed discretely, the accuracy of the generated image varies spatially. By performing imaging while continuously moving the imaging region of the subject, the medical image diagnostic system according to the sixth embodiment can reduce spatial variations in the accuracy of the generated image.

  Processing performed by the medical image diagnostic system according to the sixth embodiment will be described with reference to FIGS. 3 and 12. FIG. 12 is a diagram illustrating setting of imaging conditions according to the medical image diagnostic system according to the sixth embodiment.

  In the sixth embodiment, similarly to the first embodiment, the process described in the flowchart of FIG. 3 is performed. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  The second gantry device 2 is performed using a continuous photographing method. The processing circuit 5 receives a predetermined parameter related to the continuous shooting method as a shooting condition. In step S <b> 101, for example, the processing circuit 5 receives an input of the total imaging time “4 minutes” for the region “head” as the imaging condition corresponding to the region of the subject by the reception function 35. Further, the processing circuit 5 receives an input of the total imaging time “1 minute” for the region “lower limb” as an imaging condition corresponding to the region of the subject by the reception function 35. Further, the processing circuit 5 accepts an input of the total imaging time “2 minutes” for the region “other” as the imaging condition according to the region of the subject by the reception function 35.

  As shown in FIG. 12, in the sixth embodiment, by performing the same processing as in the first embodiment, in step S104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 12, the processing circuit 5 specifies the region “head” as the imaging range 140 </ b> A by the specifying function 33. The processing circuit 5 specifies the region “lower limb” as the imaging range 140 </ b> C by the specifying function 33. The processing circuit 5 specifies the part “others” as the imaging range 140 </ b> B by the specifying function 33.

  In the sixth embodiment, in step S <b> 105, the processing circuit 5 sets a predetermined parameter related to the continuous shooting method by the setting function 32.

  The processing circuit 5 sets the total imaging time “4 minutes” as the imaging condition in the imaging range 140 </ b> A specified as the part “head” by the setting function 32. Similarly, the processing circuit 5 sets the total imaging time “1 minute” as the imaging condition in the imaging range 140 </ b> C specified as the region “lower limb” by the setting function 32. Similarly, the processing circuit 5 sets the total imaging time “2 minutes” as the imaging condition in the imaging range 140 </ b> B specified as the part “others” by the setting function 32. The processing circuit 5 performs imaging using the continuous imaging method based on the imaging conditions set in this way.

  Thus, in the sixth embodiment, the processing circuit 5 sets a predetermined parameter related to the continuous shooting method by the setting function 32. By performing the continuous imaging method, an image with a desired accuracy can be obtained for each part in a state where the accuracy of the generated image is spatially uniform. However, if the operator manually sets the parameters for each part in the continuous imaging method, the burden on the operator is large. According to the medical image diagnostic system according to the sixth embodiment, the burden on the operator can be reduced while taking advantage of the continuous imaging method.

(Seventh embodiment)
In the seventh embodiment, the processing circuit 5 accepts input of reconstruction conditions for collected data as an imaging condition (imaging condition for each of a plurality of parts) according to a part by the reception function 35. The processing circuit 5 sets the imaging condition corresponding to the part of the second imaging based on the received imaging condition input by the setting function 32.

  Processing performed by the medical image diagnostic system according to the seventh embodiment will be described with reference to FIGS. 3 and 13. FIG. 13 is a diagram for describing setting of imaging conditions according to the medical image diagnostic system according to the sixth embodiment.

  In the seventh embodiment, similarly to the first embodiment, the processing described in the flowchart of FIG. 3 is performed. Hereinafter, a detailed description of a portion that performs the same processing as in the first embodiment will be omitted.

  In step S <b> 101, for example, the processing circuit 5 accepts an input of a reconstruction condition related to the head with respect to the part “head” as an imaging condition corresponding to the part of the subject by the accepting function 35. In addition, the processing circuit 5 uses the reception function 35 to perform whole body imaging (parts excluding the head) as a radiographing condition corresponding to the part of the subject with respect to the part “whole body (parts excluding the head)”. An input of such reconstruction conditions is accepted. Here, specific examples of the reconstruction condition include the number of iterations and the number of subsets of the OSEM method described above.

  As shown in FIG. 13, in the seventh embodiment, by performing the same processing as in the first embodiment, in step S <b> 104, the processing circuit 5 uses the specifying function 33 to specify the specified feature point. A predetermined part of the subject is identified based on the position. In the example of FIG. 13, the processing circuit 5 specifies the region “head” as the imaging range 150 </ b> B by the specifying function 33. The processing circuit 5 uses the specifying function 33 to specify the part “whole body (part excluding the head)” as the imaging range 150C.

  In the seventh embodiment, in step S <b> 105, the processing circuit 5 uses the setting function 32 to set a data reconstruction condition corresponding to a part as an imaging condition. Specifically, the processing circuit 5 sets the reconstruction condition for the head as the imaging condition in the imaging range 150 </ b> A specified as the region “head” by the setting function 32. Similarly, the processing circuit 5 uses the setting function 32 to re-record the whole body (part excluding the head) as the imaging condition in the imaging range 150C specified as the part “whole body (part excluding the head)”. Set the configuration condition input.

  In step S109, the processing circuit 5 generates a functional image based on the reconstruction condition set in step S105.

  Thus, in the seventh embodiment, the processing circuit 5 sets the reconstruction condition by the setting function 32. Since the required image accuracy differs for each part, it is desirable to set an image reconstruction condition for each part. However, if the operator manually sets these parameters, the burden on the operator is large. According to the medical image diagnostic system according to the seventh embodiment, the burden on the operator can be reduced.

(Other embodiments)
In the medical image diagnostic system according to the embodiment, the case where the first gantry device 1 is a gantry of the X-ray CT apparatus and the second gantry device 2 is the gantry of the PET apparatus has been described, but the modality is not limited thereto. . For example, the first gantry device 1 may be a gantry included in a magnetic resonance imaging apparatus. Further, the second gantry device 2 may be a gantry included in the SPECT device.

  In the medical image diagnosis system according to the embodiment, an embodiment in which only the morphological image diagnosis apparatus is independently extracted and configured is also possible. For example, the morphological image diagnosis apparatus extracts a feature point from a morphological image acquired by imaging to identify a part, and based on that, sets imaging conditions corresponding to the part in the second imaging performed by the functional image diagnostic apparatus. It may be set. Specifically, the processing circuit 5 included in the morphological image diagnostic apparatus includes a first generation function 11, a specific function 33, and a setting function 32. The processing circuit 5 uses the first generation function 11 to generate a morphological image based on the first imaging for the subject P. The processing circuit 5 uses the specifying function 33 to specify the position of the feature point of the subject P from the morphological image, and specifies the site of the subject P based on the specified position of the feature point. The processing circuit 5 uses the setting function 32 to set the imaging condition corresponding to the part of the second imaging performed for generating the functional image for the part specified by the specifying function 33.

  The morphological image diagnosis apparatus includes a gantry device (for example, the first gantry device 1) and a processing circuit 5. The gantry device collects morphological images. The processing circuit 5 acquires information related to the position of the part of the subject based on the morphological images collected by the gantry device. The processing circuit 5 controls the gantry device that captures a nuclear medicine image of the subject P based on the information related to the position of the part of the subject and the imaging conditions for each of the plurality of parts.

  In addition, in the medical image diagnostic system according to the embodiment, an embodiment in which only the functional image diagnostic apparatus (nuclear medicine diagnostic image apparatus) is extracted and configured independently is also possible. For example, a functional image diagnostic apparatus (nuclear medicine diagnostic imaging apparatus) extracts feature points from a morphological image acquired from a morphological image diagnostic apparatus, identifies a part of a subject, and performs imaging according to the part based on the feature point. A functional image may be generated by setting and shooting a condition. The processing circuit 5 included in the functional image diagnostic apparatus (nuclear medicine diagnostic image apparatus) includes a specifying function 33, a setting function 32, and a second generation function 12. The processing circuit 5 specifies the position of the feature point of the subject P from the morphological image generated by the first imaging of the subject P by the specifying function 33, and based on the position of the specified feature point, the subject The site of P is specified. The processing circuit 5 sets the imaging conditions corresponding to the part of the second imaging for the part specified by the specifying function 33. The processing circuit 5 uses the second generation function 12 to generate a functional image based on the second imaging performed according to the imaging conditions corresponding to the part.

  The nuclear medicine image diagnostic apparatus includes a processing circuit 5 and a gantry device (for example, the second gantry device 2). The processing circuit 5 acquires a morphological image from a morphological image diagnostic apparatus that collects morphological images in the subject P. The gantry device captures a nuclear medicine image of the subject P. The processing circuit 5 acquires information related to the position of the part of the subject P based on the morphological image, and controls the gantry device based on the information related to the position of the part and the imaging conditions for each of the plurality of parts.

  As described above, according to the medical image diagnostic system according to the embodiment, the burden on the operator can be reduced.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, and changes can be made without departing from the spirit of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and the equivalents thereof.

5 ... Processing circuit 11 ... First generation function 12 ... Second generation function 33 ... Specific function 32 ... Setting function

Claims (14)

In a medical image diagnostic system having a morphological image diagnostic apparatus and a nuclear medicine image diagnostic apparatus,
Based on the morphological images collected by the morphological image diagnostic apparatus, an acquisition unit that acquires information related to the position of the site of the subject;
A gantry device for taking a nuclear medicine image of the subject;
A medical image diagnostic system comprising: a control unit that controls the gantry device based on information on the position of the part and imaging conditions for each of the plurality of parts. A specifying unit for specifying the position of the feature point of the subject from the morphological image, and for specifying the site of the subject based on the specified position of the feature point;
A setting unit for setting shooting conditions for shooting by the gantry device;
Further comprising
The control unit controls the gantry device based on the information related to the position of the identified part and the imaging conditions for each of the set parts.
The medical image diagnosis system according to claim 1, further comprising an image generation unit that generates a nuclear medicine image based on the imaging performed according to imaging conditions.   The medical image diagnosis system according to claim 1, further comprising a storage circuit that stores imaging conditions for each part in imaging by the gantry device. A reception unit that receives an input of the imaging condition according to the part;
The medical image diagnosis system according to claim 1, further comprising a setting unit configured to set the imaging condition based on the accepted input of the imaging condition. The specifying unit specifies a position of the feature point of the subject from the morphological image, specifies a plurality of parts of the subject based on the specified position of the feature point,
The setting unit sets imaging conditions corresponding to each of the plurality of parts of the imaging for each of the plurality of specified parts,
The image generation unit generates the nuclear medicine image based on the imaging performed in accordance with the imaging conditions corresponding to each of the plurality of regions;
The medical image diagnostic system according to claim 2.   The medical image diagnosis system according to claim 1, further comprising a reception unit that receives an input of an imaging time or an imaging speed as the imaging condition for each of the plurality of parts.   The reception unit receives, as the imaging condition for each of the plurality of parts, an input of the size of an overlapping area of each imaging when performing the imaging for the part by dividing the imaging into a plurality of times of imaging. Item 5. The medical image diagnostic system according to Item 4.   The medical image diagnosis system according to claim 4, wherein the reception unit receives an input of a reconstruction condition of collected data as the imaging condition for each of the plurality of parts.   The medical image diagnosis system according to claim 4, wherein the reception unit receives an input of an imaging condition for synchronous imaging as the imaging condition for each of the plurality of parts.   The medical image diagnosis system according to claim 4, wherein the reception unit receives input of imaging conditions for dynamic imaging as the imaging conditions for each of the plurality of parts.   The medical image diagnosis system according to claim 1, further comprising a setting unit that sets a size of FOV (Field OfView) as the imaging condition for each of the plurality of regions.   The medical image diagnosis system according to claim 1, wherein the imaging is continuous imaging performed by continuously moving an imaging region of the subject. An acquisition unit that acquires the morphological image from a morphological image diagnostic apparatus that collects the morphological image in the subject;
A gantry device for taking a nuclear medicine image of a subject,
The acquisition unit acquires information related to the position of the part of the subject based on the morphological image, and the gantry device based on the information related to the position of the part and a plurality of imaging conditions for each of the parts A nuclear medicine diagnostic imaging device that controls A gantry device for collecting morphological images;
An acquisition unit that acquires information related to the position of the part of the subject based on the morphological image collected by the gantry device;
The acquisition unit controls a gantry device that captures a nuclear medicine image of a subject based on information on the position of the part and imaging conditions for each of a plurality of parts.
Morphological image diagnostic device.

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