Medical image processing apparatus and medical image processing method

Abstract

To generate an image over a wide range suitable for diagnosis.SOLUTION: A medical image processing apparatus includes an acquisition unit, an extraction unit, a reconfiguration unit, and an image processing unit. The acquisition unit acquires first projection data on a first region together with first dynamic state data, and acquires second projection data on a second region together with second dynamic state data. When the first and second dynamic state data exceeds a threshold and is of the same magnitude of movement, the extraction unit extracts first and second projection data sets from the first and second projection data respectively at a predetermined time phase interval or according to the magnitude, and when the first and second dynamic state data exceeds the threshold and is of different magnitudes, the extraction unit extracts the first and second projection data sets from the first and second projection data respectively according to the magnitude of the movement. The reconfiguration unit reconfigures first and second volume data on the basis of the first and second projection data sets respectively. The image processing unit combines the first and second volume data and generates combined volume data corresponding to an imaging range.SELECTED DRAWING: Figure 15

Description

[Technical field]

[0001] The embodiments disclosed in this specification and the drawings relate to a medical image processing apparatus and a medical image processing method. [Background technology]

[0002] Conventionally, as an imaging technique using an X-ray computed tomography apparatus, for example, dynamic imaging of the entire lung field of a subject is performed by using an area detector to perform dynamic imaging of the upper and lower lungs respectively. As a result, conventional imaging techniques include a technique for linking volume data generated by dynamic imaging performed on the upper and lower lungs respectively.

[0003] With the size of the current area detector, for example, when performing dynamic imaging of the entire lung field, it is difficult to image the entire lung field at once. Therefore, when performing dynamic imaging of the entire lung field, it is necessary to perform imaging two or more times. In this case, in order to link the volume data of the upper and lower lungs, it is necessary to match the breathing depth and breathing speed when imaging the upper and lower lungs. However, it is difficult to perform imaging two or more times with the breathing depth and breathing speed being the same. Therefore, dynamic images covering a wide range, such as the entire lung field, may not be suitable for diagnosis. [Prior art documents] [Patent documents]

[0004] [Patent Document 1] JP 2012-19892 A [Patent Document 2] JP 2011-172804 A [Patent Document 3] JP 2020-182524 A Summary of the Invention [Problem to be solved by the invention]

[0005] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to generate a wide range of images suitable for diagnosis. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problem. Problems corresponding to the effects of each configuration shown in the embodiments described later can also be positioned as other problems. [Means for solving the problem]

[0006] A medical image processing apparatus according to an embodiment includes an acquisition unit, an extraction unit, a reconstruction unit, and an image processing unit. The acquisition unit acquires first projection data on a first region of an imaging range of a subject together with first dynamic data on a movement of the subject, and acquires second projection data on a second region of the imaging range different from the first region together with second dynamic data on the movement. The extraction unit extracts a first projection data set corresponding to an angle range required for image reconstruction from the first projection data at a predetermined time interval or according to the magnitude, and extracts a second projection data set corresponding to the angle range from the second projection data at the same time interval as the first projection data set or for the same magnitude of the motion as the magnitude of the motion related to the first projection data set, when the first motion data and the second motion data both exceed the threshold and the magnitudes are different, extracts the first projection data set from the first projection data according to the magnitude of the motion, and extracts the second projection data set from the second projection data for the same magnitude of the motion as the magnitude of the motion related to the first projection data set. The reconstruction unit reconstructs first volume data based on the first projection data set, and reconstructs second volume data based on the second projection data set. The image processing unit generates connected volume data corresponding to the imaging range by connecting the first volume data and the second volume data. [Brief description of the drawings]

[0007] [Figure 1]FIG. 1 is a diagram showing an example of the arrangement of an X-ray CT apparatus according to an embodiment. [Diagram 2] FIG. 2 is a diagram showing an example of the inside of a stand according to the embodiment. [Diagram 3] FIG. 3 is a diagram showing abdominal movement accompanying respiratory movement in the embodiment. [Figure 4] FIG. 4 is a diagram showing an example of the appearance of a respiration sensor formed by combining a laser length measuring device and a laser control unit according to an embodiment. [Diagram 5] FIG. 5 is a diagram showing an example of a relationship between a respiratory waveform generated by a respiratory sensor and a trigger signal in one respiratory cycle according to an embodiment. [Figure 6] FIG. 6 is a diagram showing an example of a relationship between a respiratory waveform generated by a respiratory sensor and a trigger signal in a plurality of respiratory cycles according to an embodiment. [Figure 7] FIG. 7 is a diagram showing an example of a dynamic respiratory scan according to the embodiment. [Figure 8] FIG. 8 is a diagram showing an example of a dynamic respiratory scan according to the embodiment. [Figure 9] FIG. 9 is a diagram showing an example of a dynamic respiratory scan according to the embodiment. [Figure 10] FIG. 10 is a diagram showing an example of a first respiratory waveform and a second respiratory waveform when the amplitude exceeds a threshold in the embodiment. [Figure 11] FIG. 11 is a diagram showing an example of a first respiratory waveform and a second respiratory waveform when the amplitude exceeds a threshold in the embodiment. [Figure 12] FIG. 12 is a diagram showing an example of a first respiratory waveform and a second respiratory waveform in an asynchronous difference amplitude according to the embodiment. [Figure 13] FIG. 13 is a diagram showing an example of a first respiratory waveform and a second respiratory waveform in case A according to the embodiment. [Figure 14] FIG. 14 is a diagram showing an example of a first respiratory waveform and a second respiratory waveform in case B according to the embodiment. [Figure 15] FIG. 15 is a flowchart showing an example of a procedure of linked data generation processing according to the embodiment. [Figure 16]FIG. 16 is a flowchart showing an example of a procedure of linked data generation processing according to the embodiment. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0008] Hereinafter, a medical image processing device and a medical image processing method will be described with reference to the drawings. The medical image processing device according to this embodiment will be described as being mounted on an X-ray computed tomography (CT) device. Note that the medical image processing device is not limited to being mounted on an X-ray CT device, and may be realized as various server devices such as a server for a medical image management system (Picture Archiving and Communication System: PACS) or a server for an image interpretation system.

[0009] In the embodiment, the parts with the same reference numerals perform the same operation, and the duplicated description will be omitted as appropriate. Note that the embodiment is not limited to an X-ray CT device, and may be a radiation diagnostic device such as a combined device of a nuclear medicine diagnostic device such as PET (Positron Emission Tomography) and SPECT (Single Photon Emission Computed Tomography) and an X-ray CT device. The X-ray CT device in the following description will be described as an integral type X-ray CT device, but is not limited thereto, and may be realized as a photon counting type X-ray CT device.

[0010] There are various types of X-ray CT devices, such as a ROTATE / ROTATE type in which the X-ray tube and X-ray detector are integrated and rotate around the subject, and a STATIONARY / ROTATE type in which many detection elements are arranged in a ring shape and only the X-ray tube rotates around the subject, but this embodiment can be applied to any of these types. Here, the ROTATE / ROTATE type will be described.

[0011] This embodiment further includes a dynamic data acquisition device that acquires data on the movement of the subject P. The dynamic data acquisition device acquires dynamic data indicating the dynamics of the subject P as data on the movement of the subject. The dynamic data is data indicating the periodic movement of the subject P, such as breathing, walking, etc. Hereinafter, for the sake of specificity, the dynamic data acquisition device is assumed to be a breathing sensor that measures the breathing of the subject. The breathing sensor may be referred to as a breathing monitoring device that monitors the breathing of the subject. Note that the dynamic data acquisition device is not limited to a breathing sensor, and may be realized by a known dynamic monitoring device, such as a camera that measures the walking movement of the subject's legs. In this case, the linked data generation process described later may be used, for example, in the medical field of orthopedics.

[0012] (Embodiment) Fig. 1 is a diagram showing an example of the configuration of an X-ray CT apparatus 1 according to an embodiment. As shown in Fig. 1, the X-ray CT apparatus 1 includes a gantry 100, a high-voltage generator 109, and a medical image processing apparatus 40. The high-voltage generator 109 may be mounted on the gantry 100. The preprocessing apparatus 106 may be provided separately from the medical image processing apparatus 40. Fig. 2 is a diagram showing an example of the inside of the gantry 100.

[0013] As shown in FIG. 1 and FIG. 2, a gantry 100 is mounted with a ring-shaped or disk-shaped rotating frame 102 for scanning a subject P with X-rays. The rotating frame 102 is driven and rotated by a gantry drive unit 107. The rotating frame 102 supports a cone-beam X-ray tube 101 and an X-ray detector (also called a two-dimensional detector or an area detector) 103 so that they can rotate around the subject P. Specifically, the cone-beam X-ray tube 101 and the X-ray detector 103 are mounted on the rotating frame 102 so as to face each other across an imaging region S centered on the Z axis. The gantry drive unit 107 rotates the rotating frame 102 and rotates the X-ray tube 101 and the X-ray detector 103 around the subject P under the control of a host controller 110 in the medical image processing device 40.

[0014] The Z axis is defined as the rotation axis of the rotating frame 102. The Y axis is defined as the axis connecting the X-ray focal point of the X-ray tube 101 and the center of the detection surface of the X-ray detector 103. In other words, the Y axis is perpendicular to the Z axis. The X axis is defined as the axis perpendicular to the Y axis and the Z axis. In this way, the XYZ Cartesian coordinate system forms a rotating coordinate system that rotates with the rotation of the X-ray tube 101.

[0015] The X-ray tube 101 generates cone-shaped X-rays when a high voltage is applied from a high voltage generator 109. The X-ray tube 101 is, for example, a vacuum tube that generates X-rays by irradiating thermoelectrons from a cathode (filament) to an anode (target) when a high voltage is applied from the high voltage generator 109 and a filament current is supplied. X-rays are generated when the thermoelectrons collide with the target. X-rays generated at the tube focus of the X-ray tube 101 pass through an X-ray radiation window in the X-ray tube 101 and are shaped, for example, into a cone beam shape via a collimator, and are irradiated onto the subject P. The X-ray tube 101 may be, for example, a rotating anode type X-ray tube that generates X-rays by irradiating a rotating anode with thermoelectrons.

[0016] The high voltage generator 109 applies a high voltage to the X-ray tube 101 under the control of the host controller 110. The high voltage generator 109 has electric circuits such as a transformer and a rectifier, and has a high voltage generating circuit having a function of generating a high voltage to be applied to the X-ray tube 101 and a filament current to be supplied to the X-ray tube 101, and an X-ray control device that controls an output voltage according to the X-rays irradiated by the X-ray tube 101. The high voltage generator 109 may be of a transformer type or an inverter type. The high voltage generator 109 may be provided on the rotating frame 102, or may be provided on the fixed frame side of the gantry 100. The high voltage generator 109 may be called an X-ray high voltage device.

[0017] The X-ray detector 103 detects X-rays generated from the X-ray tube 101 and transmitted through the subject P, and generates a current signal according to the intensity of the detected X-rays. The X-ray detector 103 may be of a type called an area detector or a multi-row detector. This type of X-ray detector 103 is equipped with a plurality of X-ray detection elements arranged two-dimensionally. For example, 1000 X-ray detection elements are arranged along an arc centered on the Z axis. The arrangement direction of the X-ray detection elements is called the channel direction. A plurality of X-ray detection elements arranged along the channel direction is called an X-ray detection element row. For example, the row of 64 or 320 X-ray detection elements is arranged along the slice direction indicated by the Z axis. A data acquisition circuit (DAS: Data Acquisition System) 104 is connected to the X-ray detector 103.

[0018] The data collection circuit 104 reads out a current signal for each channel from the X-ray detector 103 under the control of the host controller 110. The data collection circuit 104 amplifies the read out current signal and generates projection data, which is a digital signal, by digitally converting the amplified current signal. The generated projection data is supplied to the medical image processing device 40 via a non-contact data transmission device 105. The data collection circuit 104 is provided with an IV converter for converting the current signal of each channel of the X-ray detector 103 into a voltage, an integrator for periodically integrating this voltage signal in synchronization with the X-ray exposure cycle, an amplifier for amplifying the output signal of the integrator, and an analog-to-digital converter for converting the output signal of the preamplifier into a digital signal, for each channel.

[0019] A bed 113 is installed near the gantry 100. The bed 113 has a top 111, a top support mechanism, and a top drive unit. A subject P is placed on the top 111. The top support mechanism supports the top 111 so that it can move along the Z axis. Typically, the top support mechanism supports the top 28 so that the long axis of the top 111 is parallel to the Z axis. For example, the top drive unit drives the top support mechanism under the control of the host controller 110 to move the top 111 along the Z axis direction.

[0020] A respiratory sensor 120 is connected to the medical image processing device 40 via, for example, a cable. The respiratory sensor 120 measures the respiratory movement of the subject P. Typically, in order to measure the respiratory movement of the subject P, the respiratory sensor 120 measures the movement of the abdomen accompanying the respiratory movement.

[0021] FIG. 3 is a diagram showing abdominal movement accompanying respiratory movement. As shown in FIG. 3, the abdomen usually expands with inspiration and contracts with expiration. The position and shape of internal organs also change with respiratory movement. For example, the position and shape of the lung field change significantly with breathing. That is, the position of a tumor occurring in the lung field also changes significantly with breathing. Here, the time from one inspiration to the next inspiration is called a respiratory cycle. The respiratory cycle changes depending on the way the subject P breathes, and is not constant, and the time changes for each respiratory cycle. Note that the definition of the respiratory cycle according to this embodiment is not limited to this, and for example, the time from one expiration to the next expiration may be one respiratory cycle.

[0022] The respiratory sensor 120 may be, for example, a combination of a laser length measuring device that uses a laser to measure the movement of the abdomen of the subject P and a laser controller that controls the laser. The laser controller is realized by a known computer or the like. The respiratory sensor 120 is, for example, provided in the X-ray CT device 1 as a respiratory phase measuring device that measures the respiratory phase of the subject P. The respiratory phase measuring device has a function of measuring the respiratory movement of the subject P shown in Figs. 3 and 5. As is well known, the respiratory movement is the expansion and contraction of the lung field accompanying the reciprocating motion of the diaphragm. The abdomen moves back and forth in association with the expansion and contraction of the lung field.

[0023] FIG. 4 is a diagram showing an example of the external appearance of the respiratory sensor 120 configured by combining the laser length measuring device 128 and the laser control unit 129. The laser control unit 129 has a processing circuit and a memory for controlling the laser and the like. As shown in FIG. 4, the laser length measuring device 128 in the respiratory sensor 120 is supported by a multi-joint arm 130 installed on the tabletop 111 or the like in order to detect, for example, the reciprocating movement of the abdomen. The laser length measuring device 128 has, for example, a laser generator and a photodetector. The angle of each joint of the multi-joint arm 130 is adjusted by the user so that the laser length measuring device 128 is disposed at a position and in a direction in which the laser is irradiated substantially parallel to the direction of the reciprocating movement of the abdomen of the subject P.

[0024] As shown in FIG. 4, the laser control unit 129 operates the laser generator and the photodetector of the laser length measuring device 128. At the same time, the laser control unit 129 processes the signal of the reflected light from the abdominal surface of the subject P, and repeatedly calculates the distance between the laser generator and the abdominal surface of the subject P in real time based on the time from the laser irradiation to the reception of the reflected light or the phase change of the reflected light signal. Typically, the laser control unit 129 monitors the distance between the laser generator and the abdominal surface of the subject P in real time, and generates a respiratory waveform indicating the time change of the measured value of the distance. In addition, the laser control unit 129 monitors the measured value in real time, and generates a trigger signal when the respiratory movement of the subject P reaches a specific respiratory phase on the respiratory waveform. The trigger signal is set to be generated at a specific one of a plurality of respiratory phases. The respiratory waveform data and the trigger signal are supplied to the medical image processing device 40 of the X-ray CT device 1.

[0025] The respiration sensor 120 may be a device that wraps a band around the abdomen, attaches a pressure sensor between the band and the abdomen, and observes the state of respiration based on changes in pressure. The respiration sensor 120 may also be a device that attaches a light reflecting material to the abdomen, photographs the image with a camera, and observes the state of respiration based on the movement of the light reflecting material. Any device other than the above may be used here as long as it observes the state of inhalation and exhalation.

[0026] 5 is a diagram showing an example of the relationship between the respiratory waveform generated by the respiratory sensor 120 and the trigger signal in one respiratory cycle. As shown in FIG. 5, the respiratory waveform is a graph in which the horizontal axis is defined as time and the vertical axis is defined as a measurement value. The measurement value is set, for example, so that the higher the position of the abdominal surface is, the larger the value, and the lower the position of the abdominal surface is, the smaller the value. The measurement value represents the distance between the laser generator and the abdominal surface of the subject P, which is repeatedly output from the laser control unit 129, as a peak value.

[0027] Fig. 6 is a diagram showing an example of the relationship between the respiratory waveform generated by the respiratory sensor 120 and the trigger signal in multiple respiratory cycles. As shown in Figs. 5 and 6, the distance is expressed as a wave height value that increases with inhalation and a wave height value that decreases with exhalation, but the relationship between breathing and wave height value is not limited thereto. Here, the description will be given assuming that the wave height value increases with inhalation and a wave height value that decreases with exhalation. In addition, the respiratory waveform may be a time variation in displacement from a reference distance, for example, a distance at the start of measurement, instead of a change in absolute value of the distance.

[0028] The trigger signal is generated, for example, when the measured value reaches the peak of the respiratory waveform or its vicinity. In this case, the trigger signal corresponds to the respiratory phase at the time when the subject P is breathing the deepest. The laser control unit 129 displays a mark indicating a trigger on the respiratory waveform on the monitor of the respiratory sensor 120.

[0029] The respiratory sensor 120 according to this embodiment is not limited to a type that uses a laser length measuring device 128. For example, the respiratory sensor 120 may be a type that uses a pressure sensor. In this case, the pressure sensor is attached between the abdomen of the subject P and a band wrapped around the abdomen. The pressure sensor repeatedly measures the pressure acting between the band and the abdomen. The measured values ​​are supplied to a computer connected to the pressure sensor. This computer monitors the measured values ​​from the pressure sensor and measures the pressure change to measure respiratory movement.

[0030] Furthermore, the respiratory sensor 120 according to this embodiment may be of a type that uses an optical camera. In this case, the optical camera repeatedly captures images of a light reflecting material placed on the abdomen. Image data from the optical camera is supplied to a computer connected to the optical camera. This computer monitors the position of the light reflecting material based on the image data from the optical camera, and measures the respiratory movement by measuring the movement of the light reflecting material.

[0031] The respiratory sensor 120 according to the present embodiment is not limited to the above-mentioned type. The respiratory sensor 120 according to the present embodiment may be of any type as long as it can measure the respiratory movement (the state of exhalation and the state of inhalation) of the subject P.

[0032] The medical image processing device 40 has a preprocessing device 106, a host controller 110, a memory 112, an input device 115, a display device 116, and a processing circuitry 117. The processing circuitry 117 has an acquisition function 131, a determination function 133, an extraction function 135, a reconstruction function 137, an image processing function 139, a notification function 141, and the like. Note that the processing contents realized by the preprocessing device 106 may be realized by the processing circuitry 117. In this case, the processing circuitry 117 has the preprocessing function executed by the preprocessing device 106, and the preprocessing device 106 becomes unnecessary.

[0033] The preprocessing device 106 performs preprocessing on the data detected by the data acquisition circuit 104, such as correcting uneven sensitivity between channels and correcting extreme reduction in signal intensity or signal loss caused by strong X-ray absorbers, mainly metal parts. The data (projection data) preprocessed by the preprocessing device 106 is stored in a memory 112. The projection data is associated with attribute information related to the position and timing of data acquisition, such as a time code corresponding to the data acquisition time, a channel number code, a view angle code, a rotation count code, and a tabletop position code, under the control of the host controller 110.

[0034] The host controller 110 controls the gantry driver 107, the high voltage generator 109, the data acquisition circuitry 104, the preprocessing device 106, and the like so as to execute a scan according to scan conditions set via the input device 115, etc. The host controller 110 controls the processing circuitry 117, etc. so as to reconstruct volume data according to reconstruction conditions set via the input device 115, etc. Note that various functions executed by the host controller 110 may be realized by the processing circuitry 117. At this time, the processing executed by the host controller 110 is realized, for example, by a system control function in the processing circuitry 117. The processing circuitry 117 and the host controller 110 that realize the system control function correspond to a system control unit.

[0035] In order to execute a dynamic scan over approximately one respiratory cycle, the host controller 110 realizes a scanning method specific to this embodiment, i.e., a dynamic scan synchronized with respiration (hereinafter referred to as a respiratory-gated dynamic scan). For example, in response to a trigger signal derived from a specific respiratory phase in a respiratory waveform indicating the respiratory movement of the subject P, the host controller 110 executes a respiratory-gated scan synchronized with the respiratory movement of the subject P.

[0036] Specifically, the host controller 110 controls the generation of X-rays from the X-ray tube 101 and the collection of projection data by the data collection circuitry 104 in synchronization with a trigger signal from the respiratory sensor 120 in order to dynamically scan the subject P over approximately one respiratory cycle (i.e., to repeatedly scan the same scan area over approximately one respiratory cycle while keeping the scan position fixed).

[0037] Furthermore, in order to perform dynamic scanning of each of a plurality of scan regions of the subject P over approximately one respiratory cycle (i.e., to repeatedly perform scanning at each scan position over approximately one respiratory cycle while intermittently moving the top 111 to each scan position, in other words, to repeat dynamic scanning and top movement), the host controller 110 controls the generation of X-rays from the X-ray tube 101, the collection of projection data by the data acquisition circuit 104, and the intermittent movement of the top 111 by the bed 113 in synchronization with a trigger signal from the respiratory sensor 120. That is, the host controller 110 executes a volume scan (respiratory synchronized dynamic scan) on a first region and a second region of the imaging range of the subject P as a respiratory synchronized scan.

[0038] The memory 112 is a storage device such as an HDD (Hard disk Drive), an SSD (Solid State Drive), or an integrated circuit storage device that stores various information. The memory 112 may be a drive device that reads and writes various information between the memory 112 and a portable storage medium such as a CD (Compact Disc), a DVD (Digital Versatile Disc), or a flash memory, or a semiconductor memory element such as a RAM (Random Access Memory), in addition to an HDD or SSD. The storage area of ​​the memory 112 may be in the medical image processing device 40 as shown in FIG. 1, or in an external storage device connected via a network. The memory 112 stores projection data that has been preprocessed by the preprocessing device 106. The memory 112 also stores a respiratory waveform. Specifically, the memory 112 stores the projection data in association with the phase of the respiratory waveform (for example, the peak value of the respiratory waveform).

[0039] The input device 115 is realized by an input interface. The input interface accepts various instructions and information input from a user. The input interface is realized by, for example, a trackball, a switch button, a mouse, a keyboard, a touch pad that performs an input operation by touching an operation surface, a touch screen in which a display screen and a touch pad are integrated, a non-contact input circuit using an optical sensor, and a voice input circuit. The input interface converts an input operation received from a user into an electric signal and outputs it to the processing circuitry 117. Note that the input interface in this specification is not limited to only those having physical operation parts such as a mouse and a keyboard. For example, an electric signal processing circuit that receives an electric signal corresponding to an input operation from an external input device provided separately from the medical image processing device 40 and outputs the electric signal to the processing circuitry 23 is also included as an example of the input interface.

[0040] The display device 116 displays a display image. The display device 116 also displays a setting screen for setting a scan plan for respiratory gated dynamic scanning. As the display device 116, for example, a CRT display, a liquid crystal display, an organic EL display, a plasma display, or the like can be appropriately used. The display device 116 may be called a display or a monitor. The display device 116 displays a sagittal image and / or a coronal image and a respiratory waveform side by side. The display device 116 may further display an axial image side by side at the same time. The display device 116 may further display a position along the long axis direction (z direction) of the top board 111 with respect to the respiratory waveform.

[0041] The processing circuit 117 has, as hardware resources, a processor such as a CPU, MPU, or GPU (Graphics Processing Unit), and a memory such as a ROM or RAM. The processing circuit 117 executes an acquisition function 131, a determination function 133, an extraction function 135, a reconstruction function 137, an image processing function 139, a notification function 141, and the like, by a processor that executes a program deployed in its own memory. These functions are not limited to being realized by a single processing circuit. A processing circuit may be configured by combining a plurality of independent processors, and each processor may execute a program to realize the above-mentioned plurality of functions.

[0042] For the sake of concrete explanation, the imaging range in the respiratory gated dynamic scan is assumed to be the lung field of the subject P. In this case, the imaging range has a first region corresponding to the upper lung of the subject P and a second region corresponding to the lower lung of the subject P. The first region and the second region are assumed to partially overlap each other. Note that the imaging range is not limited to two regions, the first region and the second region, and may be three or more regions.

[0043] 7 to 9 are diagrams showing an example of respiratory dynamic scanning. As shown in Fig. 7 and Fig. 8, in respiratory gated dynamic scanning, scanning and movement of the top board of the bed 113 are alternately repeated. The top board movement distance (unit distance) per one time is set to a relative distance on the Z axis according to the X-ray cone angle of the sensitivity width in the Z axis direction of the X-ray detector 103 so that the projection data is continuously connected in the Z axis direction and no gaps (blank sections) are generated in the projection data.

[0044] According to the peak value data output from the respiratory sensor 120, the host controller 110 repeats scanning with X-ray irradiation during the period from the time when the peak value passes the inhalation peak and first reaches a peak value corresponding to, for example, 100% of the respiratory phase to the time when the peak value passes the expiratory bottom and first reaches a peak value corresponding to the same respiratory phase. Note that the host controller 110 may repeat scanning with X-ray irradiation during the period from the time when the peak value passes the expiratory bottom (the minimum value of the respiratory waveform) and first reaches a peak value corresponding to, for example, 0% of the respiratory phase to the time when the peak value passes the inhalation peak and first reaches a peak value corresponding to the same respiratory phase.

[0045] Next, the host controller 110 moves the top 111 while X-ray irradiation is stopped. Typically, the rotation of the X-ray tube 101 continues even during the top movement period. After the top 111 moves the above unit distance and stops, the host controller 110 repeats scanning with X-ray irradiation during the period of the respiratory cycle from the time when the peak value first reaches a peak value corresponding to 100% of the respiratory phase to the time when the peak value next reaches a peak value corresponding to the same respiratory phase. In this way, projection data is collected over the entire imaging region while alternately repeating scanning and top movement under respiratory synchronization.

[0046] Regarding the extraction process of the projection data set for image reconstruction, a projection data set of 360° or 180°+fan angle centered on a time corresponding to a predetermined time interval or a time corresponding to a predetermined interval of the magnitude of the movement (peak value of the respiratory waveform) is extracted from the projection data generated according to the scan. The process of extracting the projection data set from the projection data will be described later.

[0047] As shown in Fig. 9, for example, the scan period can be expanded forward and backward from the time of the end of the scan period, here the time of 100% respiratory phase, so that projection data for 360° or 180°+fan angle is available. The expanded period is the time Δt required for the X-ray tube 101 to rotate an angle of 180° or 90°+(fan angle / 2).

[0048] The processing circuit 117 acquires, by the acquisition function 131, first projection data on a first region of the imaging range of the subject P together with first dynamic data on the movement of the subject P. When the imaging range is the lung field of the subject P, the movement of the subject P is a movement accompanying breathing, and the first dynamic data corresponds to a first respiratory waveform. The first projection data is generated by a first scan on the first region of the imaging range. The acquisition function 131 acquires the first projection data on the first region from the pre-processing device 106, and simultaneously acquires a first respiratory waveform corresponding to a collection period of the first projection data from the respiratory sensor 120. The acquisition function 131 associates the first projection data with the first respiratory waveform and stores them in the memory 112. The first projection data is acquired on the first region, for example, over at least one period of the first respiratory waveform.

[0049] The processing circuitry 117 acquires second projection data for a second region of the imaging range of the subject P together with second dynamic data for the movement of the subject P by the acquisition function 131. When the imaging range is the lung field of the subject P, the movement of the subject P is a movement accompanying breathing, and the second dynamic data corresponds to a second respiratory waveform. The second projection data is generated by a second scan for the second region of the imaging range. The acquisition function 131 acquires the second projection data for the second region from the pre-processing device 106, and simultaneously acquires the second respiratory waveform corresponding to the collection period of the second projection data from the respiratory sensor 120. The acquisition function 131 associates the second projection data with the second respiratory waveform and stores them in the memory 112. The second projection data is acquired for the second region, for example, over the same time phase as the first respiratory waveform, and over at least one period of the second respiratory waveform. The processing circuitry 117 that realizes the acquisition function 131 corresponds to an acquisition unit.

[0050] The processing circuitry 117 judges whether or not both the first and second respiratory waveforms exceed a threshold value by the judgment function 133. The threshold value corresponds to a predetermined depth of breathing by the subject P during the acquisition period of the first projection data and the second projection data. That is, the judgment function 133 judges whether both the first and second respiratory waveforms exceed a predetermined respiratory depth, that is, whether or not the subject P is breathing beyond the predetermined depth. The processing circuitry 117 that realizes the judgment function 133 corresponds to a judgment unit.

[0051] In addition, the processing circuit 117 uses the determination function 133 to determine whether the magnitude of the movement of the subject P in the first respiratory waveform is the same as the magnitude of the movement of the subject P in the second respiratory waveform. The magnitude of the movement of the subject P in the first respiratory waveform corresponds to the magnitude of the amplitude in the first respiratory waveform, that is, the depth of breathing. Also, the magnitude of the movement of the subject P in the second respiratory waveform corresponds to the magnitude of the amplitude in the second respiratory waveform, that is, the depth of breathing. In other words, the determination function 133 determines whether the first respiratory waveform and the second respiratory waveform are both at the same depth (depth of breathing within a specified range). Furthermore, the determination function 133 determines whether the first respiratory waveform and the second respiratory waveform are synchronized.

[0052] When it is determined that both the first respiratory waveform and the second respiratory waveform exceed the threshold and that the amplitudes (depth of respiratory class) of the first respiratory waveform and the second respiratory waveform are the same (hereinafter referred to as same amplitude exceeding the threshold), the processing circuit 117, by the extraction function 135, extracts a first projection data set corresponding to the angle range required for image reconstruction from the first projection data at a predetermined time phase interval or according to the magnitude based on the first respiratory waveform, and extracts a second projection data set corresponding to the angle range from the second projection data at the same time phase interval as the first projection data set or for a magnitude of movement that is the same as the magnitude of the movement related to the first projection data set, based on the second dynamic data.

[0053] That is, when the amplitude exceeds the threshold, the extraction function 135 extracts a plurality of first projection data sets from the first projection data corresponding to a plurality of time phases or a plurality of amplitudes in the first respiratory waveform. In addition, when the amplitude exceeds the threshold, the extraction function 135 extracts a plurality of second projection data sets from the second projection data at a time phase that is the same as the plurality of time phases in the first respiratory waveform or at the same amplitude as the amplitude in the first respiratory waveform. Then, the extraction function 135 stores the extracted first projection data set and second projection data set in the memory 112 in chronological order together with the first respiratory waveform and the second respiratory waveform. The processing circuit 117 that realizes the extraction function 135 corresponds to a determination unit.

[0054] Specifically, when the amplitude exceeds the threshold and the first respiratory waveform and the second respiratory waveform are synchronized, the processing circuit 117 causes the extraction function 135 to extract a first projection data set from the first projection data at a predetermined time phase interval based on the first respiratory waveform, and extract a second projection data set from the second projection data at the same time phase interval based on the second respiratory waveform.

[0055] FIG. 10 is a diagram showing an example of the first and second respiratory waveforms in the same amplitude above threshold. As shown in FIG. 10, the same amplitude above threshold corresponds to the case where the upper and lower lungs are scanned at the same depth beyond the set depth. In addition, in FIG. 10, the first and second respiratory waveforms are synchronized. Therefore, FIG. 10 shows a state where the upper and lower lungs are imaged at the same time in the time direction. At this time, the extraction function 135 extracts the first projection data set from the first projection data and extracts the second projection data set from the second projection data at the same predetermined time interval because the time phase and the respiratory depth are the same in the first and second respiratory waveforms as shown in FIG. 10.

[0056] In addition, when the amplitude exceeds the threshold and the first respiratory waveform and the second respiratory waveform are asynchronous, the extraction function 135 extracts a first projection data set from the first projection data at a predetermined movement interval, and extracts a second projection data set from the second projection data for the same movement as the movement of the subject P with respect to the first projection data set based on the second dynamic data.

[0057] FIG. 11 is a diagram showing an example of the first and second respiratory waveforms in the same amplitude above the threshold. As shown in FIG. 11, the same amplitude above the threshold corresponds to the case where the upper and lower lungs are scanned at the same depth beyond the set depth. In addition, in FIG. 11, the same amplitude above the threshold and the first and second respiratory waveforms are not synchronized. Therefore, as shown in FIG. 11, the first and second respiratory waveforms are not in phase in the time direction, one is early and the other is late. However, as shown in FIG. 11, the respiratory depth is the same, so the extraction function 135 extracts the first projection data set from the first projection data at a predetermined interval of movement, i.e., a predetermined interval in the respiratory phase of the vertical axis in FIG. 11, and extracts the second projection data set from the second projection data for the same movement (same respiratory phase) as the movement for the first projection data set.

[0058] When the first respiratory waveform and the second respiratory waveform both exceed the threshold and it is determined that the amplitudes (depth, magnitude of respiratory class) of the first respiratory waveform and the second respiratory waveform are different (hereinafter referred to as above-threshold difference amplitude), the processing circuit 117, by the extraction function 135, extracts a first projection data set from the first projection data in accordance with the magnitude of the movement (respiratory waveform) of the subject P based on the first respiratory waveform, and extracts a second projection data set from the second projection data in accordance with the magnitude of movement that is the same as the magnitude of movement for the first projection data set, based on the second respiratory waveform.

[0059] Specifically, when the difference amplitude exceeds the threshold and the first and second respiratory waveforms are synchronized (hereinafter referred to as case A), the extraction function 135 identifies multiple time phases at the same amplitude in the first and second respiratory waveforms. Next, the extraction function 135 extracts multiple first projection data sets corresponding to the identified multiple time phases from the first projection data, and extracts multiple second projection data sets corresponding to the identified multiple time phases from the second projection data. Next, the extraction function 135 stores the extracted first projection data set and second projection data set in the memory 112 in chronological order together with the first and second respiratory waveforms. The above extraction process in case A is hereinafter referred to as depth-first extraction.

[0060] FIG. 12 is a diagram showing an example of the first and second respiratory waveforms in the asynchronous difference amplitude. As shown in FIG. 12, the threshold exceeding same amplitude corresponds to the case where the upper and lower lungs are scanned at different depths beyond the set depth. In addition, in FIG. 12, the first and second respiratory waveforms are synchronized. That is, FIG. 12 shows a state where the upper and lower lungs are photographed at the same time in the time direction. At this time, the extraction function 135 extracts the first projection data set and the second projection data set from the first projection data and the second projection data, respectively, in the same manner as in the case shown in FIG. 11.

[0061] In FIG. 12, the respiratory waveform (solid line) with the smaller maximum value of the respiratory phase corresponds to the first respiratory waveform RW1. In the first respiratory waveform RW1, the interval of a predetermined movement based on the maximum value of the respiratory phase, that is, the time phase corresponding to the peak of the solid respiratory waveform, is indicated by the horizontal lines in the graph in FIG. 12. A plurality of time phases corresponding to a plurality of intersections between the first respiratory waveform RW1 and a plurality of horizontal lines (respiratory position values) are specified by the extraction function 135, except for the peak V of the first respiratory waveform RW1. Next, the extraction function 135 extracts projection data included in an angle range centered on an angle corresponding to each of the plurality of time phases as a first projection data set.

[0062] 12, the second projection data set corresponding to the peak V of the first respiratory waveform RW1 is extracted as the second projection data set by, for example, extracting projection data included in an angle range centered on an angle corresponding to at least one of the two intersections (IS1, IS2) between the second respiratory waveform and the respiratory phase (horizontal axis) that is the same as the peak V of the first respiratory waveform RW1. For example, the processing circuit 117 extracts, from the second projection data by the extraction function 135, for example, second projection data (hereinafter referred to as first intersection projection data) in an angle range centered on an angle corresponding to the time phase related to the first intersection IS1 or second projection data (hereinafter referred to as second intersection projection data) in an angle range centered on an angle corresponding to the time phase related to the second intersection IS2 as the second projection data set.

[0063] Furthermore, the processing circuit 117 may calculate, for example, an average of the first intersection projection data and the second intersection projection data at each of a plurality of angles in the angle range as the second projection data set by the extraction function 135. Furthermore, the extraction function 135 may calculate, as the second projection data set, a weighted addition (or weighted average) of the first intersection projection data and the second intersection projection data according to the distance from the apex V of the first respiratory waveform RW1 to the first intersection IS1 and the distance from the apex V of the first respiratory waveform RW1 to the second intersection IS2.

[0064] In addition, in case A, the processing circuitry 117 may extract a first projection data set from the first projection data at a predetermined time phase interval based on the first respiratory waveform, and extract a second projection data set from the second projection data at the same time phase interval based on the second respiratory waveform, by the extraction function 135. The above extraction process in case A is hereinafter referred to as time-priority extraction.

[0065] FIG. 13 is a diagram showing an example of the first and second respiratory waveforms in case A. As shown in FIG. 13, the threshold-exceeding same amplitude corresponds to the case where the upper and lower lungs exceed the set depth and are scanned at different depths. In addition, in FIG. 13, the first and second respiratory waveforms are synchronized. Unlike FIG. 12, FIG. 13 shows a state where the upper and lower lungs are imaged at the same time in the time direction.

[0066] In case A, the depth-priority extraction and the time-priority extraction are set or selected according to, for example, an examination order for the subject P. For example, if the examination order is a non-contrast examination, the depth-priority extraction is set and executed. At this time, the time-priority extraction may be executed following the depth-priority extraction. Also, if the examination order is a contrast examination, the time-priority extraction is executed. At this time, the depth-priority extraction may be executed following the time-priority extraction. Also, the depth-priority extraction and the time-priority extraction may be selected by a user's instruction via the input device 115. The selection of the depth-priority extraction and / or the time-priority extraction is not limited to the above, and may be appropriately performed according to the user's desire, for example, by the user's instruction after displaying an image related to the concatenated volume data described later.

[0067] When the difference amplitude exceeds the threshold and the first and second respiratory waveforms are asynchronous (hereinafter referred to as case B), the processing circuit 117 executes depth-priority extraction by the extraction function 135. FIG. 14 is a diagram showing an example of the first respiratory waveform RW1 and the second respiratory waveform RW2 in case B. As shown in FIG. 14, case B corresponds to a case where the upper and lower lungs exceed the set depth and the phases at different depths and in the time direction do not match. FIG. 14 shows an example of depth-priority extraction. In FIG. 14, the respiratory waveform (solid line) with the smaller maximum value of the respiratory phase corresponds to the first respiratory waveform RW1. In the first respiratory waveform RW1, the interval of a predetermined movement based on the maximum value of the respiratory phase, that is, the time phase corresponding to the apex of the solid line respiratory waveform, is shown by the horizontal lines in the graph in FIG. 14. A plurality of time phases corresponding to a plurality of intersections between the first respiratory waveform RW1 and a plurality of horizontal lines (values ​​of respiratory positions) are identified by the extraction function 135, except for the apex V of the first respiratory waveform RW1. Next, the extraction function 135 extracts, for each of the multiple time phases, projection data included in an angle range centered on an angle corresponding to each of the multiple time phases as a first projection data set.

[0068] 12, in FIG. 14, with respect to two intersections (IS1, IS2) between the second respiratory waveform and the respiratory phase (horizontal axis) that is the same as the peak V of the first respiratory waveform RW1, the second intersection IS2 is closer to the peak V of the first respiratory waveform RW1 than the first intersection IS1. Therefore, the second projection data set corresponding to the peak V may be extracted as the second projection data set, for example, projection data included in an angle range centered on an angle corresponding to the time phase of the second intersection IS2. The extraction process of the second projection data set may conform to the process described in FIG. 12.

[0069] In the time-priority extraction for case B, the processing circuitry 117 may extract the first projection data set from the first projection data at a reconfigurable time phase interval, and extract the second projection data set from the second projection data at the reconfigurable time phase interval, by the extraction function 135. As shown in FIG. 14, the period of the first respiratory waveform RW1 is longer than that of the second respiratory waveform RW2. For example, when the execution time of the first scan synchronized with the first respiratory waveform RW1 is 20 seconds, the execution time of the second scan synchronized with the second respiratory waveform RW2 is 10 seconds, and the volume data is reconstructed at a reconfigurable time phase interval of 1 second, 20 pieces of volume data are reconstructed in the multiple first projection data sets. Also, 10 pieces of volume data are reconstructed in the multiple second projection data sets. Therefore, an interpolation process of the volume data is performed in the image processing function 139 described later. The interpolation process will be described later.

[0070] The processing circuitry 117 reconstructs the first volume data based on the first projection data set and reconstructs the second volume data based on the second projection data set by the reconstruction function 137. For example, as shown in FIG. 10 and FIG. 13, the reconstruction function 137 reconstructs the first volume data from the first projection data set and reconstructs the second volume data from the second projection data set according to each of the multiple time phases of the vertical line. Specifically, in the case of time-priority extraction and when the first projection data set is extracted in each of the multiple time phases, the reconstruction function 137 reconstructs the multiple first volume data corresponding to the multiple time phases based on the multiple first projection data sets corresponding to the multiple time phases. In addition, in the case of time-priority extraction and when the second projection data set is extracted in each of the multiple time phases, the reconstruction function 137 reconstructs the multiple second volume data corresponding to the multiple time phases based on the multiple second projection data sets corresponding to the multiple time phases.

[0071] In addition, when the amplitude exceeds the threshold, the first and second respiratory waveforms are asynchronous, and depth-priority extraction is performed, the processing circuit 117 reconstructs the first volume data based on the first projection data set according to multiple depths (multiple amplitudes in the respiratory waveform) and reconstructs the second volume data based on the second projection data set by the reconstruction function 137. For example, as shown in Figures 11, 12, and 14, the reconstruction function 137 reconstructs the first volume data from the first projection data set and reconstructs the second volume data from the second projection data set according to each of multiple time phases corresponding to multiple respiratory phases of the horizontal lines.

[0072] Specifically, in the case of depth-priority extraction and when a first projection data set is extracted in each of a plurality of respiratory phases, the reconstruction function 137 reconstructs a plurality of first volume data corresponding to each of the plurality of respiratory phases based on a plurality of first projection data sets corresponding to the plurality of respiratory phases. Also, in the case of depth-priority extraction and when a second projection data set is extracted in each of a plurality of respiratory phases, the reconstruction function 137 reconstructs a plurality of second volume data corresponding to each of the plurality of respiratory phases based on a plurality of second projection data sets corresponding to the plurality of respiratory phases.

[0073] The processing circuitry 117 causes the first volume data and the second volume data reconstructed by the reconstruction function 137 to be associated with each of the multiple time phases and stored in the memory 112. That is, the multiple first volume data in time series and the multiple first volume data in time series are associated with the time phase or respiratory phase of the respiratory waveform and stored in the memory 112. The processing circuitry 117 that realizes the reconstruction function 137 corresponds to a reconstruction unit.

[0074] The processing circuitry 117 generates connected volume data corresponding to the imaging range by connecting the first volume data and the second volume data according to a plurality of time phases or a plurality of respiratory phases using the image processing function 139. For example, in the case of time-priority extraction and when the first projection data set is extracted in each of the plurality of time phases, the image processing function 139 generates connected connected volume data by connecting the first volume data and the second volume data in each of the plurality of time phases. In addition, in the case of depth-priority extraction and when the first projection data set is extracted in each of the plurality of respiratory phases, the image processing function 139 generates connected volume data by connecting the first volume data and the second volume data according to a plurality of respiratory phases, i.e., a plurality of depths. The processing contents of the connection between the first volume data and the second volume data can be appropriately realized using a known registration processing or the like, and therefore a description thereof will be omitted.

[0075] In the time-priority extraction in case B, the processing circuitry 117 performs an interpolation process on the volume data using the image processing function 139 before linking the volume data. For example, the image processing function 139 performs an interpolation process using a plurality of volume data related to the dynamic data of the subject P having a shorter period of motion between the first dynamic data and the second dynamic data. As a result, the image processing function 139 generates interpolated volume data according to a plurality of time phases corresponding to the plurality of volume data related to the dynamic data of the subject P having a longer period of motion between the first dynamic data and the second dynamic data.

[0076] Specifically, as shown in FIG. 14, when the execution time of the first scan synchronized with the first respiratory waveform RW1 is 20 seconds, the execution time of the second scan synchronized with the second respiratory waveform RW2 is 10 seconds, and the volume data is reconstructed at a time phase interval of 1 second, there are 20 pieces of first volume data. On the other hand, there are 10 pieces of second volume data. For this reason, the processing circuitry 117 uses the image processing function 139 to interpolate the time phase between two pieces of second volume data adjacent in time with respect to the second volume data, which is the volume data with a faster period, to generate interpolated volume data. This allows the volume data of the same time phase as the first volume data to be associated with each other using the second volume data and the interpolated volume data. Note that the interpolation process can be performed using known image interpolation techniques such as linear interpolation, and therefore a description thereof will be omitted.

[0077] Next, the processing circuitry 117 generates concatenated volume data using the first volume data, the second volume data, and the interpolated volume data by the image processing function 139. In the above example, the first volume data is concatenated with the second volume data or the interpolated volume data according to each of the multiple time phases, thereby generating concatenated volume data. Through the above processing, the image processing function 139 generates concatenated volume data.

[0078] The processing circuitry 117 generates a display image by performing three-dimensional image processing such as volume rendering, surface volume rendering, pixel value projection processing, MPR (Multi-Planer Reconstruction) processing, and CPR (Curved MPR) processing on the concatenated volume data using an image processing function 139. For example, the image processing function 139 generates a sagittal image, coronal image, axial image, and / or oblique image of the imaging range using a planar transformation processing (MPR processing) on ​​the concatenated volume data.

[0079] Note that the image processing for the concatenated volume data is not limited to the above, and various known image processing may be performed. Furthermore, the target on which the various image processing is performed is not limited to the concatenated volume data, and may be other volume data, various two-dimensional images, etc. The image processing function 139 stores the generated concatenated volume data, various images generated by performing image processing on the concatenated volume data, etc. in the memory 112. Furthermore, the various images generated by performing image processing on the concatenated volume data, etc. are displayed on the display device 116. The processing circuit 117 that realizes the image processing function 139 corresponds to an image processing unit.

[0080] The processing circuitry 117 notifies the user of various information through the notification function 141. In the following, for the sake of specificity, the first scan for collecting the first projection data on the first region will be described as a scan performed before the second scan for collecting the second projection data on the second region. For example, when it is determined that the magnitude of the movement (respiratory phase) of the subject P in the first dynamic data (first respiratory waveform) is equal to or less than a threshold, the notification function 141 notifies the user that the first scan will be performed again (hereinafter referred to as a first rescan notification). In addition, when it is determined that the magnitude of the movement of the subject P in the first dynamic data (first respiratory waveform) exceeds a threshold and the magnitude of the movement of the subject P in the second dynamic data (second respiratory waveform) is equal to or less than a threshold, the notification function 141 notifies the user that the second scan will be performed again (hereinafter referred to as a second rescan notification).

[0081] When the notification to the user is audio, the notification function 141 outputs the audio related to the rescan notification from the speaker. When the notification to the user is an image, the notification function 141 displays the image related to the rescan notification on the display device 116. The processing circuit 117 that realizes the notification function 141 corresponds to a notification unit.

[0082] The above has described the overall configuration of the X-ray CT apparatus 1. The following describes the process for generating connected volume data (hereinafter, referred to as connected data generation process). Figures 15 and 16 are flowcharts showing an example of the procedure of the connected data generation process.

[0083] (Consolidated data generation process) (Step S151) The host controller 110 executes a first scan on the first region according to the first respiratory waveform. The pre-processing device 106 generates first projection data as the first scan is executed. As a result, the processing circuit 117 acquires the first projection data together with the first respiratory waveform by the acquisition function 131. The acquisition function 131 stores the acquired first projection data in the memory 112 in association with the first respiratory waveform.

[0084] (Step S152) The processing circuit 117 judges whether the magnitude of the first respiratory waveform, i.e., the maximum amplitude of the first respiratory waveform, exceeds the threshold value by the judgment function 133. If the magnitude of the first respiratory waveform exceeds the threshold value (YES in step S152), the process of step S154 is executed. If the magnitude of the first respiratory waveform does not exceed the threshold value (NO in step S152), the process of step S153 is executed.

[0085] (Step S153) The processing circuitry 117 notifies the user of a first rescan notification recommending that the user re-execute the first scan by the notification function 141. When a user's instruction to re-execute the first scan is input via the input device 115, the process of step S151 is executed again. The first rescan notification is executed, for example, when the depth of breathing by the subject P becomes equal to or less than a threshold value.

[0086] (Step S154) The host controller 110 executes a second scan on the second region according to the second respiratory waveform. The pre-processing device 106 generates second projection data as the second scan is executed. As a result, the processing circuit 117 acquires the second projection data together with the second respiratory waveform by the acquisition function 131. The acquisition function 131 stores the acquired second projection data in the memory 112 in association with the second respiratory waveform.

[0087] (Step S155) The processing circuit 117 judges whether the magnitude of the second respiratory waveform, i.e., the maximum amplitude of the second respiratory waveform, exceeds the threshold value by the judgment function 133. If the magnitude of the second respiratory waveform exceeds the threshold value (YES in step S155), the process of step S157 is executed. If the magnitude of the second respiratory waveform does not exceed the threshold value (NO in step S155), the process of step S156 is executed.

[0088] (Step S156) The processing circuitry 117 notifies the user of a second rescan notification recommending that the user re-execute the second scan by the notification function 141. When a user's instruction to re-execute the second scan is input via the input device 115, the process of step S154 is executed again. The second rescan notification is executed, for example, when the depth of breathing by the subject P becomes equal to or less than a threshold value.

[0089] (Step S157) The processing circuit 117 judges whether the respiratory phase (respiration depth, maximum value of the amplitude of the respiratory waveform) is the same in the first respiratory waveform and the second respiratory waveform by the judgment function 133. If the respiratory depth in the first respiratory waveform is the same as the respiratory depth in the second respiratory waveform (YES in step S157), the process of step S158 is executed. If the respiratory depth in the first respiratory waveform is not the same as the respiratory depth in the second respiratory waveform (NO in step S157), the process of step S163 is executed.

[0090] (Step S158) The processing circuit 117 judges whether the first respiratory waveform and the second respiratory waveform are synchronized or not by the judgment function 133. If the first respiratory waveform and the second respiratory waveform are synchronized (Yes in step S158), the process of step S159 is executed. If the first respiratory waveform and the second respiratory waveform are not synchronized (No in step S158), the process of step S160 is executed.

[0091] (Step S159) The processing circuitry 117 extracts a plurality of first projection data sets from the first projection data at a predetermined time interval by the extraction function 135. In addition, the extraction function 135 extracts a plurality of second projection data sets from the second projection data at the same time interval as the first projection data sets. The extraction function 135 stores the extracted plurality of first projection data sets and the extracted plurality of second projection data sets in the memory 112.

[0092] (Step S160) The processing circuitry 117 extracts a plurality of first projection data sets from the first projection data at intervals of a predetermined respiratory phase (depth of respiration) by the extraction function 135. In addition, the extraction function 135 extracts a plurality of second projection data sets from the second projection data at intervals of the same respiratory phase as the plurality of first projection data sets. The extraction function 135 stores the extracted plurality of first projection data sets and the plurality of second projection data sets in the memory 112.

[0093] (Step S161) The processing circuitry 117 reconstructs a plurality of first volume data based on a plurality of first projection data sets by the reconstruction function 137. In addition, the reconstruction function 137 reconstructs a plurality of second volume data based on a plurality of second projection data sets. The reconstruction function 137 stores the reconstructed plurality of first volume data and second volume data in the memory 112.

[0094] (Step S162) The processing circuitry 117 generates a plurality of connected volume data by linking a plurality of first volume data and a plurality of second volume data according to a time phase interval or a respiratory phase interval with the image processing function 139. For example, when a plurality of first projection data sets and a plurality of second projection data sets are extracted according to a time phase interval of a respiratory waveform, the image processing function 139 links the first volume data and the second volume data according to a time phase interval to generate connected volume data. When a plurality of first projection data sets and a plurality of second projection data sets are extracted according to a respiratory phase interval, the image processing function 139 links the first volume data and the second volume data according to a respiratory phase interval to generate connected volume data. The image processing function 139 stores the generated plurality of connected volume data in the memory 112.

[0095] (Step S163) The processing circuit 117 judges whether the first respiratory waveform and the second respiratory waveform are synchronized or not by the judgment function 133. If the first respiratory waveform and the second respiratory waveform are synchronized (Yes in step S163), the process of step S164 is executed. If the first respiratory waveform and the second respiratory waveform are not synchronized (No in step S163), the process of step S165 is executed.

[0096] (Step S164) When depth-first extraction is selected by a user instruction via the input device 115 and / or a description in the examination order (YES in step S164), the process of step S150 is executed. When depth-first extraction is not selected by a user instruction via the input device 115 and / or a description in the examination order (NO in step S164), the process of step S159 is executed.

[0097] (Step S165) If depth-first extraction is selected by a user instruction via the input device 115 and / or a description in the examination order (YES in step S165), the process of step S160 is executed. If depth-first extraction is not selected by a user instruction via the input device 115 and / or a description in the examination order (NO in step S165), the process of step S166 is executed.

[0098] (Step S166) The processing circuitry 117 extracts a plurality of first projection data sets from the first projection data at a reconfigurable time interval by the extraction function 135. In addition, the extraction function 135 extracts a plurality of second projection data sets from the second projection data at a reconfigurable time interval. The extraction function 135 stores the extracted plurality of first projection data sets and the extracted plurality of second projection data sets in the memory 112.

[0099] (Step S167) The processing circuitry 117 executes an interpolation process using a plurality of volume data related to the respiratory waveform having a shorter period between the first respiratory waveform and the second respiratory waveform, by the image processing function 139. The image processing function 139 generates, by the interpolation process, interpolated volume data according to a plurality of time phases corresponding to the plurality of volume data related to the respiratory waveform having a longer period between the first respiratory waveform and the second respiratory waveform. The image processing function 139 stores the generated interpolated volume data in the memory 112.

[0100] (Step S168) The processing circuitry 117 generates connected volume data using the first volume data, the second volume data, and the interpolated volume data by the image processing function 139. The image processing function 139 stores the generated connected volume data in the memory 112. This ends the connected data generation process.

[0101] The medical image processing apparatus 40 according to the embodiment described above acquires first projection data relating to a first region of an imaging range of the subject P together with first dynamic data relating to the movement of the subject P, acquires second projection data relating to a second region of the imaging range different from the first region together with second dynamic data relating to the movement of the subject P, and, when the first dynamic data and the second dynamic data both exceed a threshold value and the magnitude of the movement of the subject P in the first dynamic data is the same as the magnitude of the movement of the subject P in the second dynamic data, extracts a first projection data set corresponding to an angle range required for image reconstruction from the first projection data at a predetermined time phase interval or according to the magnitude of the movement based on the first dynamic data, and combines a second projection data set corresponding to the angle range with the first projection data set based on the second dynamic data. Extract from the second projection data at the same time interval or for a magnitude of movement that is the same as the magnitude of the movement for the first projection data set, and when both the first dynamic data and the second dynamic data exceed a threshold value and the magnitudes are different, extract from the first projection data according to the magnitude of the movement based on the first dynamic data, and extract from the second projection data for a magnitude of the movement that is the same as the magnitude of the movement for the first projection data set based on the second dynamic data, reconstruct first volume data based on the first projection data set, reconstruct second volume data based on the second projection data set, and generate concatenated volume data corresponding to the imaging range by concatenating the first volume data and the second volume data.

[0102] In addition, the medical image processing device 40 of the embodiment extracts a first projection data set from the first projection data according to a predetermined phase interval based on the first dynamic data when the first dynamic data and the second dynamic data both exceed the threshold value, the magnitude of movement of the subject P is the same in the first dynamic data and the second dynamic data, and the movement in the first dynamic data and the second dynamic data is asynchronous, and extracts a second projection data set from the second projection data at the same phase interval based on the second dynamic data; and extracts a first projection data set from the first projection data at a predetermined movement interval, and extracts a second projection data set from the second projection data for the same movement as the movement related to the first projection data set based on the second dynamic data when the first dynamic data and the second dynamic data both exceed the threshold value, the magnitude of movement of the subject P is different in the first dynamic data and the second dynamic data, and the movement in the first dynamic data and the second dynamic data is asynchronous.

[0103] In addition, the medical image processing device 40 of the embodiment extracts a first projection data set from the first projection data at a predetermined time phase interval and extracts a second projection data set from the second projection data at the same time phase interval as the first projection data set based on the second dynamic data when both the first dynamic data and the second dynamic data exceed a threshold value, the magnitude of movement of the subject P differs between the first dynamic data and the second dynamic data, and the movement in the first dynamic data and the second dynamic data is synchronized.

[0104] From these facts, according to the medical image processing apparatus 40 of the embodiment, in the case of the threshold exceeding same amplitude, the first volume data and the second volume data are reconstructed based on the first projection data set and the second projection data set extracted at the same time phase and the same time phase interval (time-priority extraction) with respect to the motion of the subject P, and the first volume data and the second volume data are linked to generate linked volume data. In addition, according to the medical image processing apparatus 40 of the embodiment, in the case of the threshold exceeding different amplitude, the first volume data and the second volume data are reconstructed based on the first projection data set and the second projection data set extracted at the same magnitude with respect to the magnitude of the motion of the subject P (depth-priority extraction), and the first volume data and the second volume data are linked to generate linked volume data.

[0105] Therefore, according to the medical image processing device 40 of the embodiment, regardless of the magnitude of movement of the subject P, dynamic images of imaging targets over a wide range suitable for diagnosing the subject P can be generated for an imaging range spanning multiple regions.

[0106] In addition, in the medical image processing device 40 of the embodiment, when the first and second dynamic data both exceed a threshold value, and it is determined that the magnitude of movement of the subject P is different in the first and second dynamic data, and the movement in the first and second dynamic data is asynchronous, the medical image processing device 40 extracts a first projection data set from the first projection data at a reconfigurable time phase interval, and extracts a second projection data set from the reconfigurable second projection data, and generates interpolated volume data according to multiple time phases corresponding to the multiple volume data related to the dynamic data of the subject P having a shorter period of movement between the first and second dynamic data by an interpolation process using multiple volume data related to the dynamic data of the subject P having a shorter period of movement between the first and second dynamic data, and generates concatenated volume data using the first volume data, the second volume data, and the interpolated volume data.

[0107] Therefore, according to the medical image processing device 40 of the embodiment, in case B where the difference amplitude is above the threshold and the first and second respiratory waveforms are asynchronous, after time-priority extraction, interpolated volume data is generated by an interpolation process using multiple volume data related to the dynamic data of the subject P with a shorter period, and connected volume data can be generated using the first volume data, the second volume data, and the interpolated volume data. As a result, according to the medical image processing device 40 of the embodiment, even if the periods of the first dynamic data and the second dynamic data are different, dynamic images of the imaging target over a wide range suitable for diagnosing the subject P can be generated for the imaging range spanning multiple regions.

[0108] From the above, the medical image processing apparatus 40 according to the embodiment can generate dynamic images of a wide range of imaging targets suitable for diagnosing the subject P, for an imaging range spanning multiple regions, regardless of the magnitude and period of the movement of the subject P. For example, the medical image processing apparatus 40 according to the embodiment can generate dynamic images without misalignment between the upper and lower lungs, even if the respiration of the subject P is shifted in the time direction and the depth of respiration of the subject P is shifted, in a respiratory-gated dynamic scan of the upper and lower lungs.

[0109] In addition, in the medical image processing device 40 of the embodiment, the first projection data is generated from a first scan of a first region, the second projection data is generated from a second scan of a second region, the first scan is performed before the second scan, and the medical image processing device 40 of the embodiment determines whether the magnitude of movement of the subject P in the first dynamic data exceeds a threshold value and the magnitude of the movement in the second dynamic data is below the threshold value, and if it is determined that the magnitude of the movement of the subject P in the first dynamic data exceeds the threshold value and the magnitude of the movement in the second dynamic data is below the threshold value, notifies the user that the second scan will be performed again.

[0110] Furthermore, in the medical image processing apparatus 40 according to the embodiment, the first projection data is generated from a first scan of a first region, the second projection data is generated from a second scan of a second region, the first scan is performed before the second scan, and the medical image processing apparatus 40 according to the embodiment determines whether the magnitude of movement of the subject P in the first dynamic data exceeds a threshold value, and if it is determined that the magnitude of the movement in the first dynamic data is equal to or less than the threshold value, notifies the user that the first scan will be performed again.

[0111] For these reasons, the medical image processing apparatus 40 according to the embodiment can notify the user to recommend re-executing a scan in which projection data corresponding to dynamic data related to a maximum value of the first dynamic data and the second dynamic data that is equal to or less than a threshold value has been acquired. As a result, the medical image processing apparatus 40 according to the embodiment can allow the user to easily grasp the necessity of re-scanning, thereby improving the efficiency of generating a wide range of images suitable for diagnosis.

[0112] (First Modification) In this modified example, the size of the imaging target is used as a determination as to whether to notify the first rescan or the second rescan. The process performed by this modified example regarding the linked data generation process is performed, for example, after step S161 and step S166.

[0113] The processing circuitry 117 calculates the size of the imaging target in the first volume data (hereinafter referred to as the first size) by the image processing function 139. For example, when the imaging target is the lungs of the subject P and the first region is the upper lung, the first size corresponds to the size of the upper lung (the size of the upper lung). The calculation of the size of the upper lung in the first volume data can be realized by a known image processing method such as segmentation processing of the upper lung for the first volume data, image recognition processing, etc., and therefore a description thereof will be omitted.

[0114] Furthermore, the processing circuitry 117 calculates the size of the imaging target in the second volume data (hereinafter referred to as the second size) by the image processing function 139. For example, when the imaging target is the lungs of the subject P and the second region is the lower lung, the second size corresponds to the size of the lower lung (the size of the lower lung). The calculation of the size of the lower lung in the second volume data can be realized by a known image processing method such as segmentation processing of the upper lung for the second volume data, image recognition processing, etc., and therefore a description thereof will be omitted.

[0115] The processing circuit 117 determines whether the first size is equal to or smaller than a predetermined size by the determination function 133. The determination function 133 also determines whether the first size exceeds the predetermined size and the second size is equal to or smaller than the predetermined size. The predetermined size is set in advance and stored in the memory 112.

[0116] If the first size is equal to or smaller than the predetermined size, the processing circuit 117 notifies the user by the notification function 141 that the first scan will be executed again, i.e., a first rescan notification. If the first size exceeds the predetermined size and the second size is equal to or smaller than the predetermined size, the notification function 141 notifies the user that the second scan will be executed again, i.e., a second rescan notification. Other processes in this application example conform to the embodiment, and therefore will not be described.

[0117] In the medical image processing device 40 according to the first modified example of the embodiment described above, the first projection data is generated by a first scan of a first region, the second projection data is generated by a second scan of a second region, the first scan is performed before the second scan, the medical image processing device 40 according to the first modified example calculates a first size of the imaging target in the first volume data, calculates a second size of the imaging target in the second volume data, determines whether the first size exceeds a predetermined size and the second size is equal to or smaller than the predetermined size, and if the first size exceeds the predetermined size and the second size is equal to or smaller than the predetermined size, notifies the user that the second scan will be performed again.

[0118] Furthermore, in a medical image processing device 40 according to a first modified example of the embodiment, the first projection data is generated by a first scan of a first region, the second projection data is generated by a second scan of a second region, the first scan is performed before the second scan, and the medical image processing device 40 according to the first modified example calculates a first size of the imaging target in the first volume data, determines whether the first size is equal to or smaller than a predetermined size, and, if the first size is equal to or smaller than the predetermined size, notifies the user that the first scan will be performed again.

[0119] The medical image-processing device 40 according to this modification can notify the user of the need for rescanning according to the size of the imaging target in the volume data reconstructed by the reconstruction function 137. As a result, the medical image-processing device 40 according to this modification can allow the user to easily understand the need for rescanning, thereby improving the efficiency of generating wide-range images suitable for diagnosis. Other effects are similar to those of the embodiment, and therefore will not be described.

[0120] (Second Modification) In this modification, at least one of a first rescan notification and a second rescan notification is notified to the user by determining whether or not the difference between the maximum value of the magnitude of the movement of the subject P in the first behavior data and the maximum value of the magnitude of the movement of the subject P in the second behavior data is greater than a predetermined value. The process performed by this modification regarding the linked data generation process is performed, for example, after step S161 and step S166.

[0121] The processing circuit 117 uses the determination function 133 to determine whether or not a difference between the maximum value of the magnitude of the movement of the subject P in the first dynamic data and the maximum value of the magnitude of the movement in the second dynamic data is greater than a predetermined value. The predetermined value is set in advance and stored in the memory 112. For example, the determination function 133 determines whether or not a difference between the maximum value of the magnitude of the movement of the upper lung in the first respiratory waveform (maximum value of respiratory phase / amplitude) and the maximum value of the magnitude of the movement of the lower lung in the second respiratory waveform (maximum value of respiratory phase / amplitude) is greater than a predetermined value, the difference corresponding to a difference in respiratory depth.

[0122] If the difference is greater than a predetermined value, the processing circuit 117 notifies the user to perform at least one of the first scan and the second scan again, i.e., notifies at least one of the first rescan notification and the second rescan notification, by the notification function 141. Other processes in this application example conform to the embodiment, and therefore will not be described.

[0123] The medical image processing device 40 according to the second variant of the embodiment described above determines whether the difference between the maximum value of the magnitude of movement of the subject P in the first dynamic data (hereinafter referred to as the first maximum value) and the maximum value of the magnitude of movement of the subject P in the second dynamic data (hereinafter referred to as the second maximum value) is greater than a predetermined value, and if the difference is greater than the predetermined value, notifies the user that at least one of the first scan and the second scan will be performed again.

[0124] According to the medical image processing device 40 of this modification, when the difference between the first maximum value and the second placement, i.e., the difference in the range of the magnitude of movement between the first dynamic data and the second dynamic data, is greater than a predetermined value, a recommendation for rescanning can be presented to the user. As a result, according to the medical image processing device 40 of this modification, the user can easily select rescanning, thereby improving the efficiency of generating a wide range of images suitable for diagnosis. Other effects are the same as those of the embodiment, and therefore will not be described.

[0125] When the technical idea of ​​this embodiment is realized in a medical image processing method, the medical image processing method acquires first projection data relating to a first region of an imaging range of a subject P together with first dynamic data relating to the movement of the subject P, acquires second projection data relating to a second region of the imaging range different from the first region together with second dynamic data relating to the movement, and, when the first dynamic data and the second dynamic data both exceed a threshold value and the magnitude of the movement in the first dynamic data is the same as the magnitude of the movement in the second dynamic data, extracts a first projection data set corresponding to an angle range required for image reconstruction from the first projection data at a predetermined time phase interval based on the first dynamic data, and extracts a second projection data set corresponding to the angle range based on the second dynamic data. Based on the first motion data, the second projection data is extracted at the same time interval as the first projection data set, and when it is determined that both the first motion data and the second motion data exceed the threshold and the magnitudes are different, the first projection data set is extracted from the first projection data according to the magnitude of the motion based on the first motion data, and the second projection data set is extracted from the second projection data for the same magnitude of the motion as the magnitude of the motion related to the first projection data set based on the second motion data, the first volume data is reconstructed based on the first projection data set, the second volume data is reconstructed based on the second projection data set, and the first volume data and the second volume data are connected to generate connected volume data corresponding to the imaging range. The processing procedure and effects of this medical image processing method are similar to those of the embodiment, so a description thereof will be omitted.

[0126] When the technical idea of ​​this embodiment is realized by a medical image processing program, the medical image processing program causes a computer to acquire first projection data relating to a first region of an imaging range of the subject P together with first dynamic data relating to the movement of the subject P, acquire second projection data relating to a second region of the imaging range different from the first region together with second dynamic data relating to the movement, and, if both the first dynamic data and the second dynamic data exceed a threshold value and the magnitude of the movement in the first dynamic data is the same as the magnitude of the movement in the second dynamic data, extract a first projection data set corresponding to an angle range required for image reconstruction from the first projection data at a predetermined time phase interval based on the first dynamic data, and extract a second projection data set corresponding to the angle range from the second dynamic data. and extracting from the second projection data at the same time interval as the first projection data set based on the motion data, and when it is determined that both the first dynamic data and the second dynamic data exceed a threshold and the magnitudes are different, extracting a first projection data set from the first projection data in accordance with the magnitude of the movement based on the first dynamic data, and extracting a second projection data set from the second projection data for a magnitude of the movement that is the same as the magnitude of the movement related to the first projection data set based on the second dynamic data, reconstructing first volume data based on the first projection data set, reconstructing the second volume data based on the second projection data set, and generating concatenated volume data corresponding to the imaging range by concatenating the first volume data and the second volume data.

[0127] In this case, the program that can cause a computer to execute the method can be stored in a storage medium such as a magnetic disk (hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), a semiconductor memory, etc., and distributed. The processing procedure and effects of the medical image processing program are the same as those in the embodiment, so the explanation will be omitted.

[0128] According to at least one of the embodiments described above, it is possible to generate a wide range of images suitable for diagnosis.

[0129] Although the present disclosure has been described with reference to some embodiments, these embodiments are presented as examples of the principles and applications of the present disclosure and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, substitutions, modifications, and combinations of embodiments can be made without departing from the spirit of the invention. These embodiments and their modifications are within the scope of the invention and its equivalents as described in the claims, as well as the scope and spirit of the invention. [Explanation of symbols]

[0130] 1 X-ray CT device 40 Medical image processing device 100 Mount 101 X-ray tube 102 Rotating Frame 103 X-ray detector (2D detector) 104 Data Acquisition Circuit 105 Non-contact data transmission device 106 Pretreatment Equipment 107 Platform drive unit 108 Slip Ring 109 High voltage generator 110 Host Controller 111 Tabletop 112 Memory 113 Bed 115 Input Device 116 Display device 117 Processing Circuit 120 Respiration Sensor 128 Laser length measuring instrument 129 Laser control unit 130 Articulated Arm 131 Acquisition Function 133 Judgment function 135 Extraction Function 137 Reconfiguration function 139 Image Processing Functions 141 Notification function

Claims

1. an acquisition unit that acquires first projection data on a first region of an imaging range of a subject together with first dynamic data on a movement of the subject, and acquires second projection data on a second region of the imaging range different from the first region together with second dynamic data on the movement; If the first motion data and the second motion data both exceed a threshold value and the magnitude of the motion is the same, extracting a first projection data set corresponding to an angle range required for image reconstruction from the first projection data at a predetermined time interval or according to the magnitude, and extracting a second projection data set corresponding to the angle range from the second projection data at the same time interval as the first projection data set or for the same magnitude of the motion as the magnitude of the motion for the first projection data set; an extracting unit that extracts the first projection data set from the first projection data according to the magnitude of the motion when the first motion data and the second motion data both exceed the threshold value and the magnitudes are different, and extracts the second projection data set from the second projection data for a magnitude of the motion that is the same as the magnitude of the motion for the first projection data set; a reconstruction unit that reconstructs first volume data based on the first projection data set and reconstructs second volume data based on the second projection data set; an image processing unit that generates connected volume data corresponding to the imaging range by connecting the first volume data and the second volume data; A medical image processing device comprising:

2. When the first movement data and the second movement data both exceed the threshold, the magnitude is the same in the first movement data and the second movement data, and the movements in the first movement data and the second movement data are synchronous, the extraction unit extracts the first projection data set from the first projection data according to the predetermined time phase interval based on the first movement data, and extracts the second projection data set from the second projection data at the same time phase interval based on the second movement data; When the first movement data and the second movement data both exceed the threshold value, the magnitudes of the first movement data and the second movement data are different, and the movements of the first movement data and the second movement data are asynchronous, the extracting unit extracts the first projection data set from the first projection data at a predetermined movement interval, and extracts the second projection data set from the second projection data for the same movement as the movement of the first projection data set based on the second movement data. The medical image processing device according to claim 1 .

3. When both the first movement data and the second movement data exceed the threshold, the magnitudes of the first movement data and the second movement data are different, and the movements of the first movement data and the second movement data are synchronized, the extracting unit extracts the first projection data set from the first projection data at the predetermined time phase interval, and extracts the second projection data set from the second projection data at the same time phase interval as the first projection data set based on the second movement data. The medical image processing device according to claim 1 .

4. When the first movement data and the second movement data both exceed the threshold, the magnitude of the first movement data is different from that of the second movement data, and the movement in the first movement data and the movement in the second movement data is asynchronous, the extraction unit extracts the first projection data set from the first projection data at a reconstructable time phase interval based on the first movement data, and extracts the second projection data set from the second projection data at the time phase interval based on the second movement data; The image processing unit includes: generating interpolated volume data corresponding to a plurality of time phases corresponding to a plurality of volume data relating to the dynamic data having a longer motion cycle of the first dynamic data or the second dynamic data by an interpolation process using a plurality of volume data relating to the dynamic data having a shorter motion cycle of the first dynamic data or the second dynamic data; generating the connected volume data using the first volume data, the second volume data, and the interpolated volume data; The medical image processing device according to claim 1 .

5. the first projection data is generated from a first scan of the first region; the second projection data is generated from a second scan of the second region; the first scan is performed before the second scan; and a notification unit configured to notify a user that the second scan should be performed again when the magnitude of the movement in the first behavioral data exceeds the threshold value and the magnitude of the movement in the second behavioral data is equal to or smaller than the threshold value. The medical image processing device according to claim 1 .

6. the first projection data is generated from a first scan of the first region; the second projection data is generated from a second scan of the second region; the first scan is performed before the second scan; The image processing unit includes: Calculating a first size of an imaging target in the first volume data; Calculating a second size of the imaging target in the second volume data; a notification unit that notifies a user that the second scan will be executed again when the first size exceeds a predetermined size and the second size is equal to or smaller than the predetermined size, The medical image processing device according to claim 1 .

7. the first projection data is generated from a first scan of the first region; the second projection data is generated from a second scan of the second region; the first scan is performed before the second scan; and a notification unit that notifies a user to perform the first scan again when the magnitude of the movement in the first behavior data is equal to or smaller than a threshold. The medical image processing device according to claim 1 .

8. the first projection data is generated from a first scan of the first region; the second projection data is generated from a second scan of the second region; the first scan is performed before the second scan; The image processing unit calculates a first size of an imaging target in the first volume data, and a notification unit that notifies a user that the first scan will be executed again when the first size is equal to or smaller than a predetermined size. The medical image processing device according to claim 1 .

9. When a difference between a maximum value of the magnitude of the movement in the first behavioral data and a maximum value of the magnitude of the movement in the second behavioral data is greater than a predetermined value, the notification unit notifies the user to re-execute at least one of the first scan and the second scan. The medical image processing apparatus according to claim 5 .

10. acquiring first projection data relating to a first region of an imaging range of a subject together with first dynamics data relating to a motion of the subject; acquiring second projection data relating to a second region of the imaging range different from the first region together with second dynamics data relating to the movement; When the first motion data and the second motion data both exceed a threshold value and the magnitude of the subject's motion is the same, a first projection data set corresponding to an angle range required for image reconstruction is extracted from the first projection data at a predetermined time phase interval based on the first motion data, and a second projection data set corresponding to the angle range is extracted from the second projection data at the same time phase interval as the first projection data set based on the second motion data; if the first motion data and the second motion data both exceed the threshold but the magnitudes are different, extracting the first projection data set from the first projection data according to the magnitude of the motion based on the first motion data, and extracting the second projection data set from the second projection data for a magnitude of the motion that is the same as the magnitude of the motion for the first projection data set based on the second motion data; reconstructing first volume data based on the first projection data set; reconstructing second volume data based on the second projection data set; generating connected volume data corresponding to the imaging range by connecting the first volume data and the second volume data; A medical image processing method comprising:

Images