Medical image processing apparatus and x-ray computer tomographic apparatus

Abstract

To easily determine a generation purpose and a generation process of a PCCT image.SOLUTION: A medical image processing apparatus includes an acquisition unit, a generation unit, and a storage unit. The acquisition unit acquires examination information including generation purpose information showing an image generation purpose and generation process information showing an image generation process according to the generation purpose on a PCCT scan. The generation unit generates a PCCT image according to the generation purpose according to the generation process on the basis of count data collected by the PCCT scan. The storage unit associates the examination information including the generation purpose information and the generation process information with the PCCT image, and stores the information in a storage device.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] The embodiments disclosed in this specification and the drawings relate to a medical image processing apparatus and an X-ray computed tomography apparatus.

Background Art

[0002] Photon Counting CT (PCCT: Photon Counting Computed Tomography) scanning can use a large number of energy bins to generate a variety of PCCT images and identify substances. To generate PCCT images for the same purpose, there are also a variety of generation processes. Therefore, it is difficult to determine the generation purpose and generation process of the obtained PCCT images only by observing and confirming the obtained PCCT images and their scanning conditions, etc.

Prior Art Documents

Patent Documents

[0003]

Patent Document 1

Patent Document 2

Summary of the Invention

Problems to be Solved by the Invention

[0004] One of the problems to be solved by the embodiments disclosed in this specification and the drawings is to easily determine the generation purpose and generation process of PCCT images. However, the problems to be solved by the embodiments disclosed in this specification and the drawings are not limited to the above problems. It is also possible to position the problems corresponding to the respective effects of each configuration shown in the embodiments described later as other problems.

Means for Solving the Problems

[0005] The medical image processing apparatus according to the embodiment includes an acquisition unit, a generation unit, and a storage unit. The acquisition unit acquires inspection information including generation purpose information representing the generation purpose of an image and generation process information representing the generation process of the image according to the generation purpose, related to a PCCT scan. The generation unit generates a PCCT image according to the generation purpose according to the generation process based on the count data collected by the PCCT scan. The storage unit associates the inspection information including the generation purpose information and the generation process information with the PCCT image and stores it in a storage device.

Brief Description of the Drawings

[0006]

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Embodiments for Carrying Out the Invention

[0007] Hereinafter, with reference to the drawings, the medical image processing apparatus and the X-ray computed tomography apparatus according to the present embodiment will be described in detail.

[0008] The X-ray computed tomography apparatus according to the present embodiment includes various types such as third-generation CT and fourth-generation CT, and any type can be applied to the present embodiment. Here, the third-generation CT is of the Rotate / Rotate-Type in which the X-ray tube and the X-ray detector rotate around the subject integrally. The fourth-generation CT is of the Stationary / Rotate-Type in which a large number of X-ray detection elements arrayed in a ring shape are fixed and only the X-ray tube rotates around the subject. Further, the X-ray computed tomography apparatus according to the present embodiment can be applied to both a single-tube type in which one pair of the X-ray tube and the X-ray detector is mounted on a rotating ring and a multi-tube type in which a plurality of pairs of the X-ray tube and the X-ray detector are mounted on the rotating ring. In the following description, it is assumed to be of the single-tube type.

[0009] The X-ray computed tomography apparatus according to the present embodiment is assumed to be a photon counting CT apparatus that executes photon counting CT (PCCT: Photon Counting Computed Tomography).

[0010] FIG. 1 is a diagram showing the configuration of an X-ray computed tomography apparatus 1 according to the present embodiment. As shown in FIG. 1, the X-ray computed tomography apparatus 1 includes a gantry 10, a couch 30, and a console 40. In FIG. 1, for convenience of explanation, the gantry 10 is illustrated at a plurality of locations, but the X-ray computed tomography apparatus 1 may be equipped with one or a plurality of gantries 10. The gantry 10 is a scanning device having a configuration for performing a PCCT scan on a subject P. The couch 30 is a transport device for placing the subject P to be subjected to X-ray CT imaging and positioning the subject P. The console 40 is a computer for controlling the gantry 10. For example, the gantry 10 and the couch 30 are installed in a CT examination room, and the console 40 is installed in a control room adjacent to the CT examination room. The gantry 10, the couch 30, and the console 40 are connected to each other in a wired or wireless manner so as to be able to communicate with each other. Note that the console 40 does not necessarily have to be installed in the control room. For example, the console 40 may be installed in the same room as the gantry 10 and the couch 30. Further, the console 40 may be incorporated into the gantry 10. The console 40 is an example of a medical image processing device.

[0011] As shown in FIG. 1, the gantry 10 includes an X-ray tube 11, an X-ray detector 12, a rotating frame 13, an X-ray high voltage device 14, a control device 15, a wedge 16, a collimator 17, and a data acquisition circuit (DAS: Data Acquisition System) 18.

[0012] The X-ray tube 11 generates X-rays. Specifically, the X-ray tube 11 includes a cathode that generates thermoelectrons, an anode that receives the thermoelectrons flying from the cathode and generates X-rays, and a vacuum tube that holds the cathode and the anode. The X-ray tube 11 is connected to the X-ray high voltage device 14 via a high voltage cable. A tube voltage is applied between the cathode and the anode by the X-ray high voltage device 14. Due to the application of the tube voltage, thermoelectrons fly from the cathode toward the anode. When thermoelectrons fly from the cathode toward the anode, a tube current flows. Due to the application of the high voltage from the X-ray high voltage device 14 and the supply of the filament current, thermoelectrons fly from the cathode (filament) toward the anode (target), and when the thermoelectrons collide with the anode, X-rays are generated. For example, the X-ray tube 11 includes a rotating anode type X-ray tube that generates X-rays by irradiating the rotating anode with thermoelectrons.

[0013] The X-ray detector 12 detects the X-rays generated from the X-ray tube 11 and passing through the subject P, and outputs an electrical signal corresponding to the energy of the detected X-rays to the data acquisition circuit 18. The X-ray detector 12 has a structure in which a plurality of X-ray detector element arrays in which a plurality of X-ray detector elements are arranged in the channel direction are arranged in a plurality in the slice direction (column direction). The X-ray detector 12 is, for example, an indirect conversion type detector having a grid, a scintillator array, and an optical sensor array. The scintillator array has a plurality of scintillators. Each scintillator generates a plurality of fluorescent photons corresponding to the energy of the incident X-ray photons. The grid is disposed on the X-ray incident surface side of the scintillator array and has an X-ray shielding plate that absorbs scattered X-rays. Note that the grid may also be called a collimator (one-dimensional collimator or two-dimensional collimator). The optical sensor array converts the plurality of fluorescent photons from the scintillator into an electrical signal having a pulse height value corresponding to the energy of the incident X-ray photons. As the optical sensor, for example, a photodiode is used.

[0014] The X-ray detector 12 may be a direct conversion type detector. As the direct conversion type X-ray detector 12, for example, a type including a semiconductor diode having electrodes attached to both ends of a semiconductor is applicable. X-ray photons incident on the semiconductor are converted into electron-hole pairs. The number of electron-hole pairs generated by the incidence of one X-ray photon depends on the energy of the incident X-ray photon. The electrons and holes are attracted to each other by a pair of electrodes formed at both ends of the semiconductor. The pair of electrodes generates an electrical signal having a pulse height value corresponding to the charge of the electron-hole pairs. One electrical signal has a pulse height value corresponding to the energy of the incident X-ray photon.

[0015] The rotating frame 13 is an annular frame that rotatably supports the X-ray tube 11 and the X-ray detector 12 around the rotation axis (Z-axis). Specifically, the rotating frame 13 supports the X-ray tube 11 and the X-ray detector 12 in opposition. The rotating frame 13 is rotatably supported around the rotation axis by a fixed frame (not shown). By rotating the rotating frame 13 around the rotation axis by the control device 15, the X-ray tube 11 and the X-ray detector 12 are rotated around the rotation axis. The rotating frame 13 rotates around the rotation axis at a constant angular velocity receiving power from the drive mechanism of the control device 15. An image field of view (FOV) is set in the opening 19 of the rotating frame 13.

[0016] In the present embodiment, the longitudinal direction of the rotation axis of the rotating frame 13 or the top plate 33 of the bed 30 in the non-tilt state is defined as the Z-axis direction, the axial direction orthogonal to the Z-axis direction and horizontal with respect to the floor surface is defined as the X-axis direction, and the axial direction orthogonal to the Z-axis direction and perpendicular to the floor surface is defined as the Y-axis direction.

[0017] The X-ray high-voltage device 14 includes a high-voltage generator and an X-ray control device. The high-voltage generator has electric circuits such as a transformer and a rectifier, and generates a high voltage applied to the X-ray tube 11 and a filament current supplied to the X-ray tube 11. The X-ray control device controls the output voltage according to the X-rays irradiated by the X-ray tube 11. The high-voltage generator may be of a transformer type or an inverter type. The X-ray high-voltage device 14 may be provided on the rotating frame 13 within the gantry 10, or may be provided on a fixed frame (not shown) within the gantry 10.

[0018] The wedge 16 adjusts the dose of X-rays irradiated on the subject P. Specifically, the wedge 16 attenuates the X-rays so that the dose of X-rays irradiated from the X-ray tube 11 to the subject P has a predetermined distribution. For example, as the wedge 16, a metal plate such as aluminum like a wedge filter or a bow-tie filter is used.

[0019] The collimator 17 limits the irradiation range of the X-rays that have passed through the wedge 16. The collimator 17 slidably supports a plurality of lead plates that shield the X-rays, and adjusts the form of the slit formed by the plurality of lead plates. Note that the collimator 17 may also be called an X-ray aperture.

[0020] The data acquisition circuit 18 collects the count data of the X-rays detected by the X-ray detector 12 for each energy bin. As an example, the data acquisition circuit 18 includes a preamplifier, a waveform shaping circuit, a pulse height discrimination circuit, and a counting circuit. The preamplifier amplifies an electrical signal having a pulse height value corresponding to the energy of the X-ray photons detected by the X-ray detector 12 at a predetermined magnification. The waveform shaping circuit shapes the waveform of the electrical signal output by the preamplifier. The pulse height discrimination circuit applies an energy threshold value corresponding to each of a plurality of energy bins to the electrical signal output by the waveform shaping circuit, and outputs an electrical pulse signal corresponding to the energy bin to which the electrical signal belongs. The counting circuit generates count data representing the count number of X-ray photons for each energy bin by counting the electrical pulse signals output from the pulse height discrimination circuit in units of view periods for each energy bin. The data acquisition circuit 18 is realized by, for example, an application specific integrated circuit (ASIC). The count data is transmitted to the console 40 via a non-contact data transmission device or the like.

[0021] The control device 15 controls the X-ray high voltage device 14 and the data collection circuit 18 to execute a PCCT scan in accordance with the control by the processing circuit 45 of the console 40. The control device 15 includes a processing circuit having a CPU (Central Processing Unit) or an MPU (Micro Processing Unit), etc., and a drive mechanism such as a motor and an actuator. The processing circuit has, as hardware resources, a processor such as a CPU and memories such as a ROM (Read Only Memory) and a RAM (Random Access Memory). Further, the control device 15 may be realized by an ASIC or a field programmable gate array (FPGA). Further, the control device 15 may be realized by another complex programmable logic device (CPLD) or a simple programmable logic device (SPLD). The control device 15 has a function of being attached to the console 40 or the gantry 10 and receiving an input signal from an input interface 43, which will be described later, to control the operations of the gantry 10 and the bed 30. For example, the control device 15 performs control to rotate the rotating frame 13 upon receiving an input signal, control to tilt the gantry 10, and control to operate the bed 30 and the top plate 33. Note that the control to tilt the gantry 10 is realized by the control device 15 rotating the rotating frame 13 about an axis parallel to the X-axis direction based on the tilt angle (tilt angle) information input by an input interface attached to the gantry 10. Note that the control device 15 may be provided on the gantry 10 or may be provided on the console 40.

[0022] The bed 30 includes a base 31, a support frame 32, a top plate 33, and a bed driving device 34. The base 31 is installed on the floor surface. The base 31 is a housing that supports the support frame 32 so as to be movable in a direction perpendicular to the floor surface (Y-axis direction). The support frame 32 is a frame provided on the upper part of the base 31. The support frame 32 supports the top plate 33 so as to be slidable along the rotation axis (Z-axis). The top plate 33 is a flexible plate on which the subject P is placed.

[0023] The bed driving device 34 is housed inside the housing of the bed 30. The bed driving device 34 is a motor or an actuator that generates power for moving the support frame 32 and the top plate 33 on which the subject P is placed. The bed driving device 34 operates according to the control by the console 40 or the like.

[0024] The console 40 has a memory 41, a display 42, an input interface 43, a communication interface 44, and a processing circuit 45. Data communication among the memory 41, the display 42, the input interface 43, the communication interface 44, and the processing circuit 45 is performed via a bus (BUS). Although the console 40 is described as being separate from the gantry 10, the gantry 10 may include the console 40 or a part of each component of the console 40.

[0025] The memory 41 is a storage device such as a HDD (Hard Disk Drive), SSD (Solid State Drive), or integrated circuit memory device that stores various information. The memory 41 stores, for example, count data and PCCT image data. In addition to HDDs, SSDs, etc., the memory 41 may be a portable storage medium such as a CD (Compact Disc), DVD (Digital Versatile Disc), or flash memory. The memory 41 may also be a drive device that reads and writes various information to and from semiconductor memory elements such as flash memory and RAM (Random Access Memory). Further, the storage area of the memory 41 may be within the X-ray computed tomography apparatus 1 or within an external storage device connected via a network. The memory 41 stores a database described later.

[0026] The display 42 displays various information. For example, the display 42 outputs a PCCT image generated by the processing circuit 45, a GUI (Graphical User Interface) for receiving various operations from the operator, and the like. Various arbitrary displays can be appropriately used as the display 42. For example, as the display 42, a liquid crystal display (LCD), a CRT (Cathode Ray Tube) display, an organic EL display (OELD), or a plasma display can be used. Further, the display 42 may be provided on the gantry 10. Also, the display 42 may be a desktop type, or may be configured as a tablet terminal or the like capable of wireless communication with the console 40 main body.

[0027] The input interface 43 receives various input operations from the operator, converts the received input operations into electrical signals, and outputs them to the processing circuit 45. For example, the input interface 43 receives from the operator collection conditions when collecting count data, reconstruction conditions when reconstructing a PCCT image, image processing conditions when generating a post-processing image from the PCCT image, and the like. As the input interface 43, for example, a mouse, a keyboard, a trackball, a switch, a button, a joystick, a touch pad, a touch panel display, etc. can be appropriately used. Note that in the present embodiment, the input interface 43 is not limited to those including physical operation components such as a mouse, a keyboard, a trackball, a switch, a button, a joystick, a touch pad, and a touch panel display. For example, a processing circuit for receiving an electrical signal corresponding to an input operation from an external input device provided separately from the apparatus and outputting this electrical signal to the processing circuit 45 is also included in the example of the input interface 43. Further, the input interface 43 may be provided on the gantry 10. Further, the input interface 43 may be configured by a tablet terminal or the like capable of wireless communication with the console 40 main body.

[0028] The communication interface 44 includes a network interface card (NIC) or the like for communicating various data via a network with external devices such as a workstation, a PACS (Picture Archiving and Communication Systems), a RIS (Radiology Information System), and a HIS (Hospital Information System).

[0029] The processing circuit 45 controls the operation of the entire X-ray computed tomography apparatus 1 in accordance with the electrical signal of the input operation output from the input interface 43. As hardware resources, the processing circuit 45 includes a processor such as a CPU and a memory such as a ROM and a RAM. The processing circuit 45 realizes various functions by a processor that executes a program developed in the memory. The various functions are not limited to being realized by a single processing circuit. It is also possible to configure a processing circuit by combining a plurality of independent processors, and each processor executes a program to realize various functions.

[0030] As shown in FIG. 1, the processing circuit 45 realizes a scan control function 51, an acquisition function 52, an image generation function 53, a storage function 54, and a display control function 55.

[0031] In the scan control function 51, the processing circuit 45 controls the gantry 10 to perform a PCCT scan on the subject P. Under the control of the processing circuit 45, the PCCT scan is performed by the gantry 10. When the PCCT scan is executed, the data acquisition circuit 18 collects count data for each of a plurality of energy bins for each view.

[0032] In the acquisition function 52, the processing circuit 45 acquires various information. As an example, the processing circuit 45 acquires various inspection information regarding the PCCT scan to be processed. The various inspection information includes at least generation purpose information and generation process information. The generation purpose information is information representing the generation purpose of the PCCT image. The generation process information is information representing the generation process of the PCCT image according to the generation purpose. The various inspection information is assumed to be set in advance in a hospital information system such as a RIS or HIS or in the X-ray computed tomography apparatus 1 or the like before the PCCT scan. Further, the processing circuit 45 may acquire the count data collected by the PCCT scan from the data acquisition circuit 18.

[0033] In the image generation function 53, the processing circuit 45 reconstructs a PCCT image corresponding to the generation purpose represented by the generation purpose information acquired by the acquisition function 52 according to the generation process represented by the generation process information acquired by the acquisition function 52, based on the count data collected by the PCCT scan of the processing target. The PCCT image means an image based on the count data collected by the PCCT scan.

[0034] Here, the PCCT image is applicable to both a two-dimensional image related to one slice or slab and a three-dimensional image related to one volume. Note that the two-dimensional image means image data composed of a plurality of pixels (picture elements) arranged in a two-dimensional space, and the three-dimensional image means image data composed of a plurality of voxels (volume elements) arranged in a three-dimensional space. Hereinafter, it is assumed that the PCCT image is a three-dimensional image.

[0035] In the storage function 54, the processing circuit 45 associates various inspection information acquired by the acquisition function 52 with the PCCT image generated by the image generation function 53 and stores it in a storage device (hereinafter, data storage device). Examples of the various inspection information associated with the PCCT image include generation purpose information and generation process information. The data storage device may be the memory 41 equipped in the X-ray computed tomography apparatus 1, or may be a storage device in an information system such as a PACS, HIS, or RIS connected via the communication interface 44.

[0036] In the display control function 55, the processing circuit 45 displays various information on the display 42. As an example, the processing circuit 45 displays various inspection information acquired by the acquisition function 52, the PCCT image generated by the image generation function 53, and the like. In this case, the processing circuit 45 may display the generation purpose information and the generation process information together with the PCCT image. Note that the processing circuit 45 converts the PCCT image into a visualization image and displays it on the display 42. As the conversion process into a visualization image, a pixel value projection method such as MIP (Maximum Intensity Projection), a multi-planar reconstruction (MPR), a volume rendering, a surface rendering, or other conversion processes from a three-dimensional image to a two-dimensional image are used. In the following description, in order to avoid complexity of the description, the visualization image and the PCCT image are not particularly distinguished and are referred to as the PCCT image.

[0037] Hereinafter, details of the X-ray computed tomography apparatus 1 will be described.

[0038] First, various inspection information according to the present embodiment will be described. The various inspection information includes detector resolution information, bin setting information, generation purpose information, and generation process information.

[0039] The detector resolution information is information representing the detector resolution corresponding to the number of bundled X-ray detection elements (the number of X-ray detection elements belonging to one collection channel of the electrical signal). The data collection circuit 18 bundles electrical signals from a plurality of X-ray detection elements for each collection channel and counts the bundled electrical signals. The detector resolution can be set, for example, to "SHR" representing ultra-high resolution or the number of bundles "1", "HR" representing high resolution or the number of bundles "4", "NR" representing normal resolution or the number of bundles "9", and the like.

[0040] The bin setting information means information regarding the setting of the energy bin, and specifically represents the number of energy bins and the energy range. The number of energy bins is not particularly limited as long as it is two or more. The energy range can be arbitrarily set for each energy bin.

[0041] FIG. 2 is a diagram showing an example of setting the number of energy bins and the energy range. In the example of FIG. 2, it is assumed that the number of energy bins is 5, and two patterns are exemplified for the energy range of each energy bin. Note that the tube voltage is 120 kVp, and it is assumed that the energy range below 30 keV is an energy range where noise is dominant.

[0042] In Pattern 1, the energy ranges of the 5 energy bins are set approximately equally. Specifically, the energy range of bin number "1" is "30 - 48 keV", the energy range of bin number "2" is "49 - 66 keV", the energy range of bin number "3" is "67 - 84 keV", the energy range of bin number "4" is "85 - 102 keV", and the energy range of bin number "5" is "102 - 120 keV". Pattern 2 is an example of setting for K-edge imaging, assuming that the K absorption edge is around 65 - 66 keV. Specifically, the energy range of bin number "1" is "30 - 60 keV", the energy range of bin number "2" is "61 - 65 keV", the energy range of bin number "3" is "66 - 70 keV", the energy range of bin number "4" is "71 - 90 keV", and the energy range of bin number "5" is "91 - 120 keV".

[0043] The bin setting information may include, in addition to the number of energy bins and the energy range, the bins used, the representative energy value, and the image weighting coefficient. The bins used represent the energy bins used for generating the PCCT image. For example, when generating a PCCT image using only the energy bin of bin number "3" in Pattern 1 of FIG. 2 above, the value of the bins used is "3".

[0044] The representative energy value means the energy value representing each energy bin and is used for energy integration. By multiplying the count data of the energy bin to be processed by the representative energy value of the energy bin, the energy integration value of the energy bin can be obtained. The representative energy value may be set to a statistical value based only on the energy range, such as the median or average value of the energy range, or may be set to a value weighted by the energy spectrum of the X-rays irradiated from the X-ray tube 11 or the X-rays detected by the X-ray detector 12 in the energy range. For example, "76 keV" may be set as the representative energy value of bin number "3" in pattern 1 of FIG. 2 above.

[0045] The image weighting coefficient is a numerical value representing the degree of enhancement or suppression of each energy bin when generating a PCCT image using the count data of a plurality of energy bins. The image weighting coefficient may be set according to the generation purpose or the like. For example, when generating a PCCT image using all the energy bins of pattern 1 in FIG. 2 above equally, the image weighting coefficient of bin number "1" is "1", the image weighting coefficient of bin number "2" is "1", the image weighting coefficient of bin number "3" is "1", the image weighting coefficient of bin number "4" is "1", and the image weighting coefficient of bin number "5" is "1". As another example, when generating a PCCT image that emphasizes components on the low-energy side such as fat, the image weighting coefficient of bin number "1" is "1", the image weighting coefficient of bin number "2" is "2", the image weighting coefficient of bin number "3" is "2", the image weighting coefficient of bin number "4" is "1 / 5", and the image weighting coefficient of bin number "5" is "1 / 5". Note that the image weighting coefficient may be "0".

[0046] The generation purpose information represents the purpose of generating the PCCT image, in other words, the type of image that the user wants to view. For example, the generation purposes include an integral image, a basis material image, a virtual monochromatic image, a material map, etc. The generation purpose may be set in more detail. For example, in the case of an integral image, the number of the used bin or the energy range such as energy bin "3" or energy range "67~84 keV" may be added. In the case of a basis material image or a material map, information on the material to be emphasized such as a basis material image or a material map of "bone" may be added. For example, in the case of a virtual monochromatic image, a virtual monochromatic energy value such as energy value "74 keV" may be added.

[0047] As described above, the generation process information represents the generation process of the image according to the generation purpose. The generation process is represented by a series of names or codes of the processes through which the image according to the generation purpose is generated. As an example, the generation process is represented by a combination of energy integral image reconstruction, material discrimination, material discrimination image reconstruction, virtual monochromatic image generation and / or material map generation. Note that the generation process may be expressed in detail by adding bin setting information such as the used bin, the representative energy value, and the image weighting coefficient in addition to the names or codes of the above-mentioned processes.

[0048] FIG. 3 is a diagram showing the details of the generation process of the PCCT image. As shown in FIG. 3, the processing circuit 45 performs preprocessing on the count data (step S1). As the preprocessing, data reformatting, beam hardening correction, etc. are performed. After step S1, the generation process is divided into two branches: the counting mode and the spectral mode. First, the counting mode will be described.

[0049] The processing circuit 45 performs counting line-integral sinogram estimation on the pre-processed count data (step S2) to generate a counting line-integral sinogram. A counting line is a virtual line that reaches each X-ray detection element (or the central element of the collection channel) of the X-rays that have passed through the subject P, and corresponds to the projection line in the integral type CT. When step S2 is performed, the processing circuit 45 performs energy integral image reconstruction on the counting line-integral sinogram (step S3) to reconstruct the integral image.

[0050] FIG. 4 is a diagram showing a specific example of the generation process in the counting mode. In FIG. 4, similar to FIG. 2, it is assumed that the number of energies is 5. As shown in FIG. 4, the processing circuit 45 generates pre-processed count data for each of energies 1 to 5. For example, for each energy bin, the processing circuit 45 generates energy integral data by multiplying and adding the energy bin representative value of the energy bin to the count data for each counting line, performs counting line-integral sinogram estimation (S2) on the generated energy integral data, and may perform FBP (Filtered Back Projection) reconstruction on the counting line-integral sinogram to reconstruct the integral image of the energy bin (S3).

[0051] As another example, as shown in FIG. 4, the processing circuit 45 performs counting line-integral sinogram estimation (S2) on the energy integral data of each of all the energy bins, and for each energy bin, generates a weighted addition counting line-integral sinogram by multiplying and adding the image weighting coefficient of the energy bin to the counting line-integral sinogram, and may perform FBP (Filtered Back Projection) reconstruction on the weighted addition counting line-integral sinogram to reconstruct the integral image of all the energy bins (S3). The values of the image weighting coefficients for a plurality of energy bins can be arbitrarily set.

[0052] As another example, as shown in FIG. 4, the processing circuit 45 may generate a difference image between the integrated image of energy bin "3" and the integrated image of energy bin "4". Note that the energy bins to be differentiated are not limited to the combination of "3" and "4", and any energy bins may be used.

[0053] Next, with reference to FIG. 3, the spectral mode will be described. The processing circuit 45 performs material discrimination on the preprocessed count data (step S4) and generates two basis material pathlength sinograms corresponding to two basis materials respectively. The material discrimination can be performed in either the data domain or the image domain. The types of the two basis materials can be set to any types as generation target information and / or generation process information. As the types of the two basis materials, for example, combinations such as bone and water, water and contrast agent (iodine), etc. are possible. Note that the number of basis materials may be set to two or more and not more than the total number of energy bins. Next, the processing circuit 45 performs material discrimination image reconstruction on the two basis material pathlength sinograms (step S5) and reconstructs two basis material images corresponding to the two basis materials respectively. The basis material image represents the spatial distribution of the corresponding basis material. Note that the pixel value of the basis material image corresponds to the density value of the basis material and is different from the CT value.

[0054] As shown in FIG. 3, the processing circuit 45 may perform virtual monochromatic image generation processing on the two basis material images (step S6) and generate a virtual monochromatic image corresponding to any X-ray energy (hereinafter referred to as virtual monochromatic energy). The value of the virtual monochromatic energy can be set to any value as generation target information and / or generation process information. The pixel value of the virtual monochromatic image is the CT value.

[0055] As shown in FIG. 3, the processing circuit 45 performs material map generation processing on the virtual monochromatic image (step S7) and generates two material maps corresponding to the two basis materials respectively. The processing circuit 45 may generate a composite image of the two material maps. The pixel value of the material map is the CT value.

[0056] Next, the processing procedure of the PCCT examination by the X-ray computed tomography apparatus 1 will be described.

[0057] FIG. 5 is a diagram showing the processing procedure of the PCCT examination by the X-ray computed tomography apparatus 1. As shown in FIG. 5, the processing circuit 45 acquires various examination information by the acquisition function 52 (step SA1). As described above, the various examination information includes generation purpose information, generation process information, bin setting information, and detector resolution information. It is assumed that the various examination information is preset at the time of the order of the PCCT examination by the RIS or the like. In this case, in step SA1, the processing circuit 45 can acquire the various examination information together with the order information from the RIS that orders the PCCT examination. Note that the various examination information can also be set by another computer system, the processing circuit 45 of the X-ray computed tomography apparatus 1, or the like. The acquired various examination information is stored in the memory 41.

[0058] When step SA1 is performed, the processing circuit 45 executes a PCCT scan by the scan control function 51 (step SA2). In step SA2, the processing circuit 45 controls the gantry 10 according to separately set scan conditions to execute a PCCT scan on the subject P. Specifically, the number and values of the energy thresholds of the data collection circuit 18 are set according to the number and energy range of the energy bins included in the bin setting information. Also, the detector resolution of the data collection circuit 18 is set according to the detector resolution included in the detector resolution information.

[0059] When step SA2 is performed, the processing circuit 45 generates a PCCT image based on the count data collected in step SA2 (step SA3). In step SA3, the processing circuit 45 generates a PCCT image that matches the generation purpose information and the generation process information. Specifically, the processing circuit 45 processes the count data in order according to the generation process represented by the generation process information, and generates a PCCT image corresponding to the generation purpose represented by the generation purpose information.

[0060] When step SA3 is performed, the processing circuit 45 displays various inspection information acquired in step S1 together with the PCCT image generated in step SA3 (step SA4). Various methods can be implemented as the method for displaying the PCCT image and the various inspection information. As an example, the processing circuit 45 superimposes and displays text representing the various inspection information on the PCCT image. The types of the various inspection information to be displayed can be arbitrarily selected via the input interface 43 or the like. The text representing the various inspection information may be set in advance by the user or the like, or may be converted from the various inspection information according to an arbitrary automatic conversion algorithm.

[0061] Hereinafter, specific examples of the display of the PCCT image and the various inspection information will be described. Here, consider the case of generating a PCCT image with a generation purpose of "equivalent to 75 keV". As the generation process of the PCCT image, as shown in FIGS. 3 and 4, for example, there are considered a pattern 1 of generating an integral image of the third energy bin corresponding to the energy range "70 to 80 keV", and a pattern 2 of generating a virtual monochromatic image of a virtual monochromatic energy "75 keV". More specifically, pattern 1 goes through the process of "using the count data of energy bin "3" to perform energy integral image reconstruction to generate an integral image". More specifically, pattern 2 goes through the process of "using all the count data of energy bins "1" to "5" to perform material discrimination, performing basis material image reconstruction to generate two basis material images corresponding to two basis materials respectively, and performing virtual monochromatic image generation processing to generate a virtual monochromatic image".

[0062] When displaying two PCCT images with the same generation purpose and different generation processes without particularly distinguishing them, there is a risk that it may not be known through which generation process each image is generated. To reduce such an adverse effect, the processing circuit 45 displays the generation purpose and the generation process together with each image.

[0063] FIG. 6 is a diagram showing an example of a display screen I1 of a PCCT image I11 with a generation target of "equivalent to 75 keV" according to the above pattern 1 and various inspection information I12. As described above, in FIG. 6, the generation target of "equivalent to 75 keV" is represented by the text "Mono 75 keV". Pattern 1 is, as described above, "using the count data of energy bin "3" to perform energy integration image reconstruction to generate an integrated image", and in FIG. 6, it is represented by the text "3bin→EI". "3bin" means using the count data of energy bin "3". "EI" means energy integration (EI: Energy Integration) image reconstruction. Also, as shown in FIG. 6, text such as "70 - 80 keV" representing the energy range and "SHR" representing the detector resolution may be displayed.

[0064] FIG. 7 is a diagram showing an example of a display screen I2 of a PCCT image I21 with a generation target of "equivalent to 75 keV" according to the above pattern 2 and various inspection information I22. As described above, in FIG. 7, the generation target of "equivalent to 75 keV" is represented by the text "Mono 75 keV". Pattern 2 is, as described above, "using all the count data of energy bins "1" to "5" to perform material discrimination, performing basis material image reconstruction to generate two basis material images corresponding to two basis materials respectively, and performing virtual monoenergetic image generation processing to generate a virtual monoenergetic image", and in FIG. 7, it is represented by the text "1 - 5bin→Md→2 - Basis(Image)→VMI". "1 - 5bin" means using the count data of energy bins "1" to "5". "Md" means material decomposition (MD: Material Decomposition), "2 - Basis(Image)" means the reconstruction process for generating two basis material images corresponding to two basis materials respectively, and "VMI" means the reconstruction process for a virtual monoenergetic image (Virtual Monoenergetic Image). Also, as shown in FIG. 7, text such as "30 - 120 keV" representing the energy range and "HR" representing the detector resolution may be displayed.

[0065] As shown in FIGS. 6 and 7, the processing circuit 45 displays text representing the generation purpose and text representing the generation process for each of the PCCT images I11 and I21. Both texts may be displayed in the margin portions of the display screens I1 and I2 other than the PCCT images I11 and I21. As can be seen by comparing FIGS. 6 and 7, even if the generation purpose "Mono 75keV" is the same, by displaying the text representing the generation process together with the PCCT image, it becomes possible to grasp the generation process and thus the characteristics of the PCCT image. For example, by checking the generation process of the image in FIG. 6, it can be seen that the displayed image is an integrated image corresponding to the third energy bin, and by checking the generation process of the image in FIG. 7, it can be seen that the displayed image is a virtual monochromatic image generated from a basis material image. Thus, when there are a plurality of PCCT images with the same generation purpose and different generation processes, by displaying the generation process together with the PCCT image, it becomes possible to reduce the risk that the user will confuse the PCCT images with each other.

[0066] Another specific example will be described. Assume that the generation purpose according to this specific example is "substance discrimination (iodine & calcium)". This generation purpose means a PCCT image using iodine and calcium as basis materials. Such PCCT images may include basis material images and substance maps.

[0067] FIG. 8 is a diagram showing a display example of a PCCT image with the generation purpose "substance discrimination (iodine & calcium)" and various inspection information. In FIG. 8, as a PCCT image with the generation purpose "substance discrimination (iodine & calcium)", a substance map (hereinafter, iodine & calcium map) representing the spatial distribution of the CT values of iodine and calcium maps is displayed. A composite image of the iodine substance map and the calcium (bone) substance map is displayed. An example of the generation procedure of the iodine & calcium map is that first, the processing circuit 45 performs threshold processing on the iodine substance map to extract the iodine region, performs threshold processing on the calcium substance map to extract the calcium region, and generates the iodine & calcium map by synthesizing the iodine region (the hatched portion in FIG. 8) and the calcium region (the dotted hatched portion in FIG. 8).

[0068] The generation process shown in FIG. 8 is "using all the count data of energy bins '1' to '5' to perform material discrimination, performing base material image reconstruction to generate two base material images corresponding to two base materials respectively, performing virtual monochromatic image generation processing to generate a virtual monochromatic image, and performing material map generation processing to generate material maps of iodine and calcium", and in FIG. 8, it is represented by the text "1-5bin→Md→2-Basis(Image)→VMI→map(Iodine,Calcium)". "1-5bin" means using the count data of energy bins '1' to '5'. "Md" means material discrimination (MD:Material Decomposition), "2-Basis(Image)" means the reconstruction process for two base material images corresponding to two base materials respectively, and "VMI" means the reconstruction for a virtual monoenergetic image (Virtual Monoenergetic Image). "map(Iodine,Calcium)" means the generation process of material maps of iodine and calcium. Also, as shown in FIG. 8, texts such as "30-120keV" representing the energy range and "SHR" representing the detector resolution may be displayed. As shown in FIG. 8, by displaying the generation process together with the material map, it is possible to avoid confusion with the base material image.

[0069] In addition, in the examples of FIGS. 6 to 8 above, it is assumed that items of various inspection information such as the generation purpose, generation process, energy range, and detector resolution are displayed. However, this embodiment is not limited thereto. The processing circuit 45 may switch the display or non-display of each item included in the various inspection information according to a user's instruction or a predetermined algorithm. Also, the PCCT images I11, I21, I31 in FIGS. 6 to 8 have a phantom as the subject, but can be appropriately replaced with images having the subject P as the subject.

[0070] When step SA4 is performed, the processing circuit 45 associates various inspection information obtained in step S1 with the PCCT image generated in step SA3 and stores it in the data storage device (step SA5). The processing circuit 45 may associate all items among the various inspection information, or may limit the association to some items among all items. The items to be associated can be arbitrarily selected according to a user's instruction or a predetermined algorithm.

[0071] FIG. 9 is a conceptual diagram of the association between the PCCT image 92 and various inspection information 93. As shown in FIG. 9, the processing circuit 45 associates the PCCT image 92 generated in step SA3 with the various inspection information 93 obtained in step SA1, and stores the associated PCCT image 92 and various inspection information 93 in the data storage device 91. The various inspection information 93 only needs to be associated with text information representing generation purpose information, generation process information, bin setting information, and detector resolution information. By associating and storing the PCCT image 92 and the various inspection information 93, it becomes possible to read out and confirm the generation purpose, generation process, etc. of the PCCT image 92 at an arbitrary timing. Therefore, it becomes possible to easily determine the generation purpose, generation process, etc. of the PCCT image 92.

[0072] As methods for associating the PCCT image and various inspection information, various methods can be selected. Hereinafter, the association methods will be exemplified. Note that the association method is not limited to the following methods.

[0073] <Method 1> The processing circuit 45 may associate the PCCT image and various inspection information by inputting the various inspection information into the comment input field of the PCCT image. The comment input field means a GUI (Graphical User Interface) component superimposed on the PCCT image. For example, generation purpose information may be input into image comment 1, generation process information may be input into image comment 2, bin setting information may be input into image comment 3, and detector resolution information may be input into image comment 4. The text input into the comment input field will be integrally displayed as an element of the PCCT image.

[0074] <Method 2> The processing circuit 45 may associate the PCCT image with various inspection information by inputting various inspection information into the data elements corresponding to the DICOM standard tags of the PCCT image.

[0075] Figure 10 is a diagram showing a first example of inputting various inspection information into DICOM standard tags. Figure 10 illustrates the data representation method (VR: Value Representation), data, and remarks column of DICOM standard tags. As bin setting information, the total number of bins, lower threshold value, upper threshold value, energy bin representative value, and image weighting coefficient are input. In the first input example, the lower threshold value, upper threshold value, energy bin representative value, and image weighting coefficient are input with different DICOM tags for each energy bin. For example, the data of the lower threshold value (VR = "BL") of the energy bin "2" is "40", the data of the upper threshold value (VR = "BU") is "60", the data of the energy representative value (VR = "EV") is "*", and the data of the image weighting coefficient (VR = "IC") is "*". As generation purpose information, the generation purpose is input. The VR of the generation purpose may be defined as "GP" or the like, and text representing the generation purpose may be input into the data. As generation process information, the generation process is input. The VR of the generation process may be defined as "GF" or the like, and text representing the generation process may be input into the data.

[0076] FIG. 11 is a diagram showing a second input example of various inspection information into DICOM standard tags. In FIG. 11, similar to FIG. 10, the data representation method, data, and remarks column of DICOM standard tags are illustrated. In the second input example, the energy bin threshold value, energy bin representative value, and image weighting coefficient are input with DICOM tags common to all energy bins. Note that the VR of the threshold value is defined by "BT" or the like, and the lower threshold value and the upper threshold value are arranged in the data in the order of the energy bins. Similarly, in the data of the energy bin representative value and the image weighting coefficient, the data values are also arranged in the order of the energy bins. For example, the data of the threshold value (VR = "BT") is "20,40,40,60,60,80,80,100,100,120", the data of the energy bin representative value (VR = "EV") is "*,*,*,*,*", and the data of the image weighting coefficient (VR = "IC") is "*,*,*,*,*,*".

[0077] Note that the input examples in FIGS. 10 and 11 are just examples, and information other than the information shown in FIGS. 10 and 11 may be input. Also, the values of VR are also examples and are not limited thereto, and may be defined by any character string.

[0078] <Method 3> The processing circuit 45 may input the association between the PCCT image and various inspection information into the data element corresponding to the DICOM private tag of the PCCT image. The VR of the DICOM private tag corresponding to the item of various inspection information can be arbitrarily set by the user.

[0079] When step SA5 is performed, the PCCT inspection according to this embodiment ends.

[0080] Note that the processing procedure of the PCCT inspection shown in FIG. 5 is just an example, and this embodiment is not limited thereto. For example, the order of step SA4 and step SA5 may be reversed. Also, either one of step SA4 and step SA5 may be omitted. Step SA1 may be executed between step SA2 and step SA3.

[0081] This embodiment is not limited to the above-described embodiment, and any element can be deleted, added, and / or modified without departing from the spirit of the invention.

[0082] (Modification Example 1) In the above embodiment, the medical image processing apparatus 40 is assumed to be a console provided in the X-ray computed tomography apparatus 1. However, this embodiment is not limited thereto. The medical image processing apparatus 40 according to Modification Example 1 may be a computer separate from the X-ray computed tomography apparatus 1 such as a reading device, an imaging device, or a workstation. In this case, the medical image processing apparatus 40 does not necessarily need to have the scan control function 51. The processing circuit 45 according to Modification Example 1 acquires the PCCT image and various inspection information from the data storage device, and displays the acquired various inspection information together with the PCCT image.

[0083] FIG. 12 is a diagram showing a processing procedure of the display processing of the PCCT image by the medical image processing apparatus 40 according to Modification Example 1. It is assumed that the PCCT image and various inspection information are stored in the data storage device before the start of FIG. 12.

[0084] As shown in FIG. 12, first, the processing circuit 45 acquires, by the acquisition function 52, the PCCT image to be displayed and various inspection information associated with the PCCT image from the data storage device (step SB1). The PCCT image to be displayed can be arbitrarily specified by the user via the input interface 43 or the like.

[0085] When step SB1 is performed, the processing circuit 45 displays, by the display control function 55, the various inspection information together with the PCCT image acquired in step SB1 on the display 42 (step SB2). In step SB2, the processing circuit 45 may superimpose text representing the various inspection information on the PCCT image as shown in FIGS. 6, 7, and 8. Thereby, it becomes possible to immediately display and confirm various inspection information such as the generation purpose and generation process of the PCCT image without confusion with other PCCT images.

[0086] The display method of various inspection information will vary according to the association method between the above PCCT image and various inspection information. For example, in the case of <Method 1>, since the text of various inspection information is input in the comment input field of the PCCT image, the text of various inspection information will be displayed as an element of the PCCT image. In the case of <Method 2>, the processing circuit 45 reads the text of various inspection information from the DICOM standard tag and superimposes and displays the read text on the PCCT image. In the case of <Method 3>, similar to <Method 2>, the processing circuit 45 reads the text of various inspection information from the DICOM private tag and superimposes and displays the read text on the PCCT image.

[0087] When step SB2 is performed, the display process according to Modification Example 1 shown in FIG. 12 ends.

[0088] According to Modification Example 1, in the medical image processing apparatus 40 independent of the X-ray computed tomography apparatus 1, it is also possible to associate and store the PCCT image and various inspection information, and to display various inspection information together with the PCCT image, similar to the above embodiment. Thereby, the generation purpose and generation process of the PCCT image can be easily grasped.

[0089] (Modification Example 2) The processing circuit 45 according to Modification Example 2 may associate inspection information including generation process information corresponding to the intermediate image with the intermediate image generated in the generation process of the PCCT image (hereinafter, generation purpose image) corresponding to the generation purpose, and store it in the data storage device. For example, in the case of FIG. 7, in the generation process of the virtual monochromatic image which is the generation purpose image, a substance discrimination image which is an intermediate image is generated. The processing circuit 45 according to Modification Example 2 associates the same generation process information as the generation process information of the virtual monochromatic image with the substance discrimination image and stores it in the data storage device. Specifically, as the generation process information, the same text "1-5bin→Md→2-Basis(Image)→VMI" as the generation process of the virtual monochromatic image is associated with the substance discrimination image which is the intermediate image.

[0090] Note that the processing circuit 45 may store the generation process information of the intermediate image in association with the intermediate image. The processing circuit 45 can generate the generation process information of the intermediate image by extracting the part corresponding to the generation process of the intermediate image from the generation process of the target image to be generated. For example, in the case of FIG. 7, it is possible to extract the text "1-5bin→Md→2-Basis(Image)" of the generation process of the substance discrimination image, which is the intermediate image, from the text "1-5bin→Md→2-Basis(Image)→VMI" of the generation process of the virtual monochromatic image, which is the target image to be generated.

[0091] The processing circuit 45 may store, in association with the intermediate image, inspection information other than the generation process information, such as generation target information, bin setting information, and detector resolution information. In this case, the generation target information, bin setting information, and detector resolution information may be the same information as that used for the target image to be generated.

[0092] (Modification Example 3) In the above embodiment, it is assumed that the generation target information and the generation process information are determined before the PCCT scan is performed. However, this embodiment is not limited thereto. The processing circuit 45 according to Modification Example 3 may determine the generation target information and the generation process information after the PCCT scan is performed. For example, the generation target information and the generation process information may be determined for the first time after the PCCT scan is performed, or after the first generation target information and the generation process information are determined before or after the PCCT scan is performed, the second generation target information different from the original target and the generation process information corresponding to the second generation target information may be determined. The processing circuit 45 according to Modification Example 3 can also store and / or display the inspection information including the second generation target information and the generation process information in association with the PCCT image generated according to the second generation target information and the generation process information.

[0093] In the above-described embodiment, as an example, the generation targets were assumed to be an integral image, a base material image, a virtual monochromatic image, and a material map. However, the present embodiment is not limited thereto. The generation target according to the present embodiment may be any image that can be generated in PCCT, such as an electron density image, an effective atomic number image, a K-edge image, or the like.

[0094] (Modification Example 4) The X-ray computed tomography apparatus 1 according to Modification Example 4 performs a PCCT scan, generates a PCCT image, and / or displays a PCCT image according to various inspection information stored in step SA5. Hereinafter, the X-ray computed tomography apparatus according to Modification Example 4 will be described.

[0095] Similar to Modification Example 1, the processing circuit 45 according to Modification Example 4 acquires, by the acquisition function 52, a PCCT image to be displayed and various inspection information associated with the PCCT image from the data storage device, and displays, by the display control function 55, the acquired PCCT image together with the various inspection information on the display 42. The PCCT image to be displayed can be arbitrarily specified by the user via the input interface 43 or the like.

[0096] Here, it is assumed that a user who has confirmed the PCCT image and various inspection information wants to perform a PCCT scan and image generation under the same conditions as the PCCT image.

[0097] Specifically, when the processing circuit 45 receives a command to execute the same scan as the various inspection information of the acquired past scan, the scan control function 51 controls the gantry 10 according to the inspection information to execute another PCCT scan (the current scan). Specifically, according to the bin setting information and the detector resolution information among the various inspection information of the past scan, the energy bin of the current scan and the detector resolution of the X-ray detector 12 are set, and the current scan is performed under the set energy bin and detector resolution. This makes it possible to perform the current scan with the same energy bin and detector resolution as the past scan.

[0098] The processing circuit 45 generates, according to the image generation function 53, other PCCT images (current images) corresponding to the generation purpose among various inspection information of the previous scan in accordance with the generation process, based on the count data collected by the current scan. Then, the processing circuit 45 displays the current images on the display 42 by the display control function 55. For example, when the generation purpose of the previous scan is "equivalent to 75 keV" and the generation process is "1-5 bin → Md → 2-Basis (Image) → VMI", the processing circuit 45 performs material discrimination on the count data of energy bins 1 to 5, generates two basis material images corresponding to two basis materials respectively, and reconstructs the virtual monochromatic image. Thereby, the current images can be generated and displayed in accordance with the same generation purpose and generation process as those of the past scan.

[0099] According to Modification 4, by diverting various inspection information of the past scan stored in association with the PCCT image for the current scan, it becomes possible to easily execute the PCCT scan and image generation under the same conditions as the past scan.

[0100] (Summary) According to some of the above embodiments, the medical image processing apparatus 40 has a processing circuit 45 that realizes an acquisition function 52, an image generation function 53, and a storage function 54. The processing circuit 45 acquires inspection information including generation purpose information representing the generation purpose of an image and generation process information representing the generation process of the image corresponding to the generation purpose, regarding the PCCT scan. The processing circuit 45 generates a PCCT image corresponding to the generation purpose in accordance with the generation process, based on the count data collected by the PCCT scan. The processing circuit 45 associates the inspection information including the generation purpose information and the generation process information with the PCCT image and stores it in the data storage device.

[0101] According to another embodiment, the medical image processing apparatus 40 includes a processing circuit 45 that realizes an acquisition function 52, an image generation function 53, and a display control function 55. The processing circuit 45 acquires inspection information including generation purpose information representing the purpose of generating an image and generation process information representing the generation process of the image according to the generation purpose, regarding the PCCT scan. The processing circuit 45 generates a PCCT image according to the generation purpose in accordance with the generation process based on the count data collected by the PCCT scan. The processing circuit 45 displays on the display 42 the inspection information including the generation purpose information and the generation process information together with the PCCT image.

[0102] According to at least one of the embodiments described above, it is possible to easily determine the generation purpose and generation process of the PCCT image.

[0103] In the above description, the term "processor" used means, for example, a CPU, a GPU, or a circuit such as an Application Specific Integrated Circuit (ASIC), a Programmable Logic Device (for example, a Simple Programmable Logic Device (SPLD), a Complex Programmable Logic Device (CPLD), and a Field Programmable Gate Array (FPGA)). The processor realizes its function by reading and executing a program stored in a storage circuit. Note that, instead of storing the program in the storage circuit, the program may be directly incorporated into the circuit of the processor. In this case, the processor realizes its function by reading and executing the program incorporated in the circuit. On the other hand, when the processor is, for example, an ASIC, instead of storing the program in the storage circuit, the function is directly incorporated as a logic circuit into the circuit of the processor. Note that each processor of the present embodiment is not limited to being configured as a single circuit for each processor, and a plurality of independent circuits may be combined to be configured as one processor to realize its function. Further, a plurality of components in FIG. 1 may be integrated into one processor to realize its function.

[0104] Although several embodiments have been described, these embodiments are presented as examples and are not intended to limit the scope of the invention. These embodiments can be implemented in various other forms, and various omissions, replacements, changes, and combinations of the embodiments can be made without departing from the gist of the invention. These embodiments and their modifications are included in the scope and gist of the invention, and are also included in the invention described in the claims and its equivalent scope.

Explanation of Reference Numerals

[0105] 1 X-ray computed tomography apparatus 10 Stand 11 X-ray tube 12 X-ray detector 13 Rotating frame 14 X-ray high voltage device 15 Control device 16 Wedge 17 Collimator 18 Data acquisition circuit (DAS) 19 Opening 30 Bed 31 Base 32 Support frame 33 Ceiling panel 34 Bed drive device 40 Console (medical imaging device) 41 Memory 42 Display 43 Input interface 44 Communication interface 45 Processing circuit 51 Scan control function 52 Acquisition function 53 Image generation function 54 Saving function 55 Display control function

Claims

1. An acquisition unit that acquires inspection information including generation purpose information representing the purpose of generating an image and generation process information representing the generation process of the image according to the generation purpose, related to a PCCT scan; A generation unit that generates a PCCT image according to the generation purpose according to the count data collected by the PCCT scan according to the generation process; A storage unit that associates the inspection information including the generation purpose information and the generation process information with the PCCT image and stores it in a storage device; A medical image processing apparatus comprising:

2. The medical image processing apparatus according to claim 1, wherein the generation process is represented by a combination of energy integration image reconstruction, material discrimination, material discrimination image reconstruction, virtual monochromatic image generation and / or material map generation.

3. The acquisition unit further acquires bin setting information representing the number of energy bins and / or the energy range in the PCCT scan, The storage unit further associates the bin setting information with the PCCT image, The medical image processing apparatus according to claim 1.

4. The medical image processing apparatus according to claim 1, further comprising a display control unit that displays the inspection information including the generation purpose information and the generation process information on a display device together with the PCCT image.

5. The display control unit according to claim 4, wherein the display control unit acquires the PCCT image and the inspection information from the storage device and displays the acquired inspection information together with the PCCT image.

6. The display control unit according to claim 4, wherein the display control unit displays text representing the generation purpose information and text representing the generation process information superimposed on the PCCT image.

7. The display control unit switches the display or non-display of each item included in the inspection information according to a user instruction or a predetermined algorithm. The medical image processing apparatus according to claim 4.

8. The storage unit inputs the inspection information into a comment input field of the reconstructed P CCT image. The medical image processing apparatus according to claim 1.

9. The storage unit inputs the inspection information into a data element corresponding to a DICOM standard tag of the reconstructed P CCT image. The medical image processing apparatus according to claim 1.

10. The storage unit inputs the inspection information into a data element corresponding to a DICOM private tag of the reconstructed P CCT image. The medical image processing apparatus according to claim 1.

11. The storage unit associates other generation process information corresponding to the intermediate image with the intermediate image generated in the generation process of the P CCT image and stores the same in the storage device. The medical image processing apparatus according to claim 1.

12. An acquisition unit that acquires inspection information including generation purpose information representing the purpose of generating an image related to P CCT scan and generation process information representing the generation process of the image corresponding to the generation purpose; A generation unit that generates a P CCT image corresponding to the generation purpose according to the generation process based on the count data collected by the P CCT scan; A display control unit that displays the inspection information including the generation purpose information and the generation process information on a display device together with the P CCT image; A medical image processing apparatus comprising:

13. A gantry having an X-ray tube that generates X-rays, an X-ray detector that detects the X-rays generated from the X-ray tube, and a data acquisition circuit that acquires count data of the X-rays detected by the X-ray detector; An acquisition unit that acquires inspection information including generation purpose information representing the purpose of generating an image related to P CCT scan and generation process information representing the generation process of the image corresponding to the generation purpose; A generation unit that generates a PCT image according to the generation purpose according to the count data collected by the data collection circuit according to the generation process; A storage unit that stores the PCT image in a storage device in association with the inspection information including the generation purpose information and the generation process information; An X-ray computed tomography apparatus comprising:

14. A display control unit that acquires the PCT image and the inspection information from the storage device and displays the acquired inspection information on a display device together with the PCT image; A scan control unit that controls the gantry to execute another PCT scan according to the acquired inspection information when receiving a command to execute the same scan as the acquired inspection information. The X-ray computed tomography apparatus according to claim 13, further comprising: The X-ray computed tomography apparatus according to claim 13.

15. The generation unit according to claim 14, wherein the generation unit generates another PCT image according to the generation purpose among the acquired inspection information according to the generation process based on the count data collected by the other PCT scan. X-ray computed tomography apparatus.

16. The X-ray computed tomography apparatus according to claim 15, wherein the display control unit displays the other PCT image on a display device.

Images