Medical diagnostic apparatus, data control method, data control program, and computer program product

Abstract

To provide a medical diagnostic apparatus, a data control method, and a data control program which are hardly affected by pile-up even during high-dose imaging.SOLUTION: The medical diagnostic apparatus includes at least one processor, and the processor acquires positioning imaging data obtained by scanography of a subject with a first dose before main imaging of the subject and main imaging data obtained by main imaging of the subject with a second dose higher than the first dose, corrects the main imaging data by specific processing using at least the positioning imaging data, and outputs the corrected imaging data.SELECTED DRAWING: Figure 3

Description

[Technical Field]

[0001] The technology of the present disclosure relates to a medical diagnostic device, a data control method, and a data control program. [Background technology]

[0002] Photon counting computed tomography (PCCT) devices equipped with detectors that employ a photon counting method are being developed (see, for example, Patent Document 1). The detectors identify the energy (wavelength) of incident radiation and count the number of times radiation is detected for each of multiple energy levels. PCCT devices can obtain more information than CT (computed tomography) devices equipped with charge integration detectors. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] Japanese Patent Application Publication No. 2024-053288 Summary of the Invention [Problem to be solved by the invention]

[0004] However, because this detector detects multiple radiation photons as a single radiation photon, it is susceptible to pile-up during imaging (main scan) when high doses are applied to collect images used for diagnosis. That is, during the main scan, the number of detected radiation counts and the energy of the incident radiation may be erroneously determined, which may result in errors in the imaging data.

[0005] In view of the above, an object of the present disclosure is to provide a medical diagnostic apparatus, a data control method, and a data control program that are less susceptible to the effects of pileup even during imaging with a high dose. [Means for solving the problem]

[0006] In order to achieve the above object, the medical diagnostic device according to the technology of the present disclosure is a medical diagnostic device equipped with at least one processor, which acquires positioning imaging data obtained by scanning the subject at a first dose before the actual imaging of the subject, and actual imaging data obtained by performing the actual imaging of the subject at a second dose higher than the first dose, corrects the actual imaging data by a specific process using at least the positioning imaging data, and outputs the corrected imaging data.

[0007] The processor acquires data obtained by synchronizing the imaging trajectory during the actual imaging with the imaging trajectory during scanning as the actual imaging data.

[0008] In the specific processing, the processor generates forward projection data of the positioning shooting data by forward projecting the positioning image contained in the acquired positioning shooting data in accordance with the trajectory of the actual shooting data, and corrects the actual shooting data using the generated forward projection data.

[0009] In the specific processing, the processor corrects the main imaging data using the difference between the positioning imaging data and the main imaging data.

[0010] In the specific processing, the processor corrects the main imaging data using the difference between the positioning imaging data and the main imaging data in the imaging data portion other than high-frequency noise contained therein.

[0011] In the identification process, the processor corrects the main imaging data using the difference between the positioning imaging data and the main imaging data, from which high frequency noise contained in each of the positioning imaging data and the main imaging data has been removed.

[0012] In the specific processing, the processor corrects the main imaging data using the difference between the imaging data portion from which noise contained in the positioning imaging data has been removed and the main imaging data.

[0013] In the specific processing, the processor estimates the magnitude of the error during the actual shooting based on the number of photons or projection value detected by the detector, and corrects the actual shooting data using the positioning shooting data to remove the estimated error.

[0014] In a specific process, if there tends to be a large difference between the positioning shooting data and the actual shooting data, the processor corrects the actual shooting data by multiplying the actual shooting data by a coefficient corresponding to the ratio between the positioning shooting data and the actual shooting data.

[0015] In the specific processing, the processor corrects the main imaging data by multiplying the main imaging data by a coefficient according to the ratio between the positioning imaging data, which tends to have low projection values ​​during scanning, and the main imaging data.

[0016] In the identification process, the processor corrects the main imaging data so that the specific representative values ​​of the positioning imaging data and the main imaging data are equal in both the positioning imaging data and the main imaging data.

[0017] In the specific processing, the processor corrects the main imaging data by mixing the low frequency components contained in the positioning imaging data with the high frequency components contained in the main imaging data.

[0018] In the specific processing, the processor compares the low-frequency components contained in the positioning shooting data and the actual shooting data, and based on the comparison results, corrects the actual shooting data so that the low-frequency components contained in the actual shooting data are closer to the low-frequency components contained in the positioning shooting data.

[0019] In the specific processing, the processor reconstructs a tomographic image of the subject by blending the positioning imaging data and the corrected main imaging data.

[0020] The data control method according to the disclosed technology is executed by a computer to acquire positioning imaging data obtained by scanning the subject at a first dose before the actual imaging of the subject, and actual imaging data obtained by performing the actual imaging of the subject at a second dose higher than the first dose, correct the actual imaging data by a specific process using at least the positioning imaging data, and output the corrected imaging data.

[0021] The data control program relating to the technology of the present disclosure causes a computer to acquire positioning imaging data obtained by scanning the subject at a first dose before the actual imaging of the subject, and actual imaging data obtained by performing the actual imaging of the subject at a second dose higher than the first dose, correct the actual imaging data by a specific process using at least the positioning imaging data, and output the corrected imaging data.

[0022] A computer program product relating to the technology of the present disclosure includes a program that causes at least one processor to execute processing including acquiring positioning imaging data obtained by scanning a subject at a first dose before the actual imaging of the subject, and actual imaging data obtained by performing the actual imaging of the subject at a second dose higher than the first dose, correcting the actual imaging data by a specific process using at least the positioning imaging data, and outputting the corrected imaging data. [Effects of the Invention]

[0023] According to the technology of the present disclosure, it is possible to reduce the influence of pile-up even during imaging with a high dose. [Brief explanation of the drawings]

[0024] [Figure 1] FIG. 1 is a configuration diagram of a medical diagnostic system 100 according to an embodiment of the present disclosure. [Figure 2] FIG. 2 is a diagram illustrating an example of the hardware configuration of the medical diagnostic apparatus 4 according to the embodiment of the present disclosure. [Figure 3] FIG. 3 is a diagram showing functional blocks of the medical diagnostic apparatus 4 according to the embodiment of the present disclosure. [Figure 4]FIG. 4 is a flowchart for explaining the operation of the medical diagnostic device 4. DETAILED DESCRIPTION OF THE INVENTION

[0025] An example of an embodiment of the present disclosure will be described below with reference to the drawings. In each drawing, the same or equivalent components and parts are designated by the same reference numerals. Furthermore, the dimensional proportions in the drawings are exaggerated for the sake of explanation and may differ from the actual proportions.

[0026] FIG. 1 is a configuration diagram of a medical diagnostic system 100 according to an embodiment of the present disclosure. The medical diagnostic system 100 may be interpreted as, for example, an X-ray CT device. Note that the medical diagnostic system 100 is not limited to an X-ray CT device, and may be a system related to other medical examinations. The medical diagnostic system 100 may include a scanner 1, a bed 3, and a medical diagnostic device 4.

[0027] (Scanner 1) The scanner 1 may be interpreted as a part that performs a CT scan. The scanner 1 may include a gantry 11, a rotating plate 12, an X-ray tube device 13, a collimator 14, an X-ray detector 15, and a rotating plate drive device 17.

[0028] The rotating plate 12 may be interpreted as a plate having an opening in the center and rotatably supported by the gantry 11. The rotating plate 12 may include a collimator control device 18, a rotating plate drive control device 19, an X-ray high voltage generator 20, a data acquisition device 16, and a data transmission device 21.

[0029] The collimator control device 18 may control the collimator 14 to change the X-ray irradiation field. The rotating plate drive control device 19 may control the drive of the rotating plate drive device 17. The X-ray high voltage generator 20 may supply power for generating X-rays to the X-ray tube device 13 and control the X-ray generation conditions. The data collection device 16 may collect the output of the X-ray detector 15. The data transmission device 21 may transmit the data collected by the data collection device 16. The supply of power and control signals to each unit provided on the rotating plate 12 and the extraction of data from each unit provided on the rotating plate 12 are performed via a slip ring (not shown) provided between the gantry 11 and the rotating plate 12.

[0030] The X-ray tube device 13 may be fixed to the rotating plate 12. The collimator 14 may be provided at the X-ray emission port of the X-ray tube device 13. The X-ray detector 15 may be arranged opposite the X-ray tube device 13 with the opening of the rotating plate 12 in between. The rotating plate driving device 17 may be provided on the gantry 11. The X-ray detector 15 may be considered to be a detector that employs a photon counting method.

[0031] (Bed 3) The bed 3 may be considered as a platform that moves the subject 6 between an imaging preparation position and an imaging position. The subject 6 is placed on a top board 31. The top board 31 has a vertical movement mechanism and a forward / backward movement mechanism, which are not shown in the figure. The bed 3 is provided with a bed controller 32, a top board vertical movement controller 33, and a top board forward / backward movement controller 34 to control the operation of the vertical movement mechanism and the forward / backward movement mechanism of the top board 31.

[0032] (Medical diagnostic equipment 4) Next, an example of the hardware configuration of the medical diagnostic device 4 will be described with reference to Fig. 2. Fig. 2 is a diagram showing an example of the hardware configuration of the medical diagnostic device 4 according to an embodiment of the present disclosure. The medical diagnostic device 4 may include a CPU (Central Processing Unit) 41, a storage unit 43 which is a non-volatile memory, a display 44 such as a liquid crystal display, an input device 45, a memory 46 which is a temporary storage area, and a network I / F (Interface) 47. The CPU 41, the memory 46, the storage unit 43, the display 44, the input device 45, and the network I / F 47 are connected to a bus 48.

[0033] The CPU 41 may be interpreted as a processor in the present disclosure. The input device 45 may include a pointing device such as a keyboard or a mouse. The storage unit 43 may be realized by a hard disk drive (HDD), a solid state drive (SSD), a flash memory, or the like. A data control program 42 may be stored in the storage unit 43. The CPU 41 may read the data control program 42 from the storage unit 43, load it into the memory 46, and execute the loaded data control program 42. The data control program 42 may be provided on a cloud server or the like.

[0034] Next, functions of the medical diagnostic device 4 will be described with reference to Fig. 3. Fig. 3 is a diagram showing functional blocks of the medical diagnostic device 4 according to the embodiment of the present disclosure. The medical diagnostic device 4 may include a data acquisition unit 4a, a data correction unit 4b, and a data output unit 4c. These functional configurations may be realized by the CPU 41 shown in Fig. 2 reading out the data control program 42 and loading it into the memory 46.

[0035] (Data acquisition unit 4a) The data acquisition unit 4a may acquire positioning imaging data obtained by scanning the subject 6 at a first dose before the actual imaging of the subject 6, and actual imaging data obtained by imaging the subject 6 at a second dose higher than the first dose.

[0036] The positioning imaging data may include projection data obtained by imaging to collect positioning images (scanograms), X-ray measurement data (detector measurement values), etc. The actual imaging data may include projection data obtained by actual imaging (scanning) to collect images to be used for observation, X-ray measurement data (detector measurement values), etc.

[0037] (Data acquisition example) The data acquiring unit 4a may acquire, as the main imaging data, data obtained by synchronizing the imaging trajectory during the main imaging with the imaging trajectory (track) during scanning.

[0038] Specifically, the actual imaging data may be acquired when the trajectory (track) of the X-ray source in helical imaging during the actual imaging is synchronized with the trajectory (track) of the X-ray source in helical imaging during scanning. Note that the subject from which the positioning imaging data acquired at a low dose and the actual imaging data acquired at a high dose are acquired may be the same subject.

[0039] Although the positioning imaging data taken at a low dose and the main imaging data taken at a high dose have significantly different X-ray detection ratios, their projection data (values ​​obtained by multiplying the attenuation coefficient of X-rays by the path length for each material through which the X-rays have passed) are essentially the same. The data corrector 4b may correct the main imaging data, for example, using the difference between the positioning imaging data and the main imaging data in which the imaging (trajectory) is synchronized. The configuration of the data corrector 4b will be described in detail later.

[0040] (Data correction unit 4b) The data correcting unit 4b may correct the main imaging data by a specific process using at least the positioning imaging data. A specific example of data correction by the data correcting unit 4b will be described below.

[0041] (Data correction example 1) In the specific processing, the data correction unit 4b may generate forward projection data of the positioning shooting data by forward projecting the positioning image contained in the acquired positioning shooting data in accordance with the trajectory of the actual shooting data, and may correct the actual shooting data using the generated forward projection data.

[0042] Specifically, the data corrector 4b performs a re-imaging (forward projection) process on the low-dose imaging data (positioning imaging data) to obtain forward projection data whose trajectory matches the trajectory of the actual imaging data (main imaging data). The forward projection data obtained from the low-dose imaging data is imaging data in which errors are unlikely to occur. Based on this forward projection data, the data corrector 4b may calculate, for example, the difference or ratio between the forward projection data whose trajectory matches and the main imaging data, and correct the main imaging data so that the difference or ratio becomes smaller.

[0043] (Data correction example 2) In the identification process, the data corrector 4b may correct the main imaging data using the difference between the positioning imaging data and the main imaging data.

[0044] For example, in the specific processing, the data corrector 4b may correct the main imaging data using the difference between the positioning imaging data (or forward projection data) and the main imaging data, except for the high-frequency noise contained therein. By taking the difference between the positioning imaging data and the main imaging data, it is possible to extract the error of the remaining component excluding the high-frequency noise contained in the main imaging data. The data corrector 4b may regard the positioning imaging data acquired at a low dose as correct data, and correct the main imaging data so as to reduce the error of the remaining component excluding the high-frequency noise contained in the main imaging data.

[0045] (Data correction example 4) In the specific processing, the data correction unit 4b may correct the actual shooting data using the difference between the positioning shooting data and the actual shooting data, from which high-frequency noise contained in each data has been removed (for example, the mid-to-low frequency range of the shooting data).

[0046] In the specific processing, the data correction unit 4b may correct the actual shooting data by using the difference between the shooting data portions from which high-frequency noise contained in the aforementioned forward projection data and the actual shooting data has been removed, instead of the positioning shooting data and the actual shooting data.

[0047] (Data correction example 5) In the identification process, the data corrector 4b may correct the main imaging data using the difference between the imaging data portion from which noise contained in the positioning imaging data has been removed and the main imaging data.

[0048] Specifically, the data correction unit 4b may reduce the noise contained in the positioning shooting data by channel averaging processing, and correct the actual shooting data using the difference between the positioning shooting data after noise reduction and the shooting data portion (e.g., the mid-low frequency range of the shooting data).

[0049] In the specific processing, the data correction unit 4b may reduce the noise contained in the aforementioned forward projection data by channel averaging processing instead of the noise contained in the positioning shooting data, and correct the actual shooting data using the difference between the forward projection data after noise reduction and the shooting data portion (for example, the mid-low frequency range of the shooting data).

[0050] (Data correction example 6) In the identification process, the data corrector 4b may estimate the magnitude of an error during actual imaging based on the number of photons or the projection value detected by the detector (X-ray detector 15), and may correct the actual imaging data using the positioning imaging data so as to remove the estimated error. The number of photons may be interpreted as the number of photons detected by the X-ray detector 15. The projection value may be interpreted as a value output by a detection element included in the X-ray detector 15 in accordance with the number of photons.

[0051] PCCT can detect the number of X-ray photons, and the ratio of the number of X-ray photons contained in the positioning imaging data and the actual imaging data corresponds to the ratio of the X-ray doses. For example, if the dose ratio between the low-dose imaging data and the high-dose imaging data is 1:2, the ratio of the number of X-ray photons will also be 1:2. Because there is a correlation between the error in the high-dose imaging data and the error in the low-dose imaging data, the data corrector 4b can estimate the magnitude of the error during the actual imaging corresponding to the ratio of the number of X-ray photons. The data corrector 4b may correct the actual imaging data using the positioning imaging data to remove the estimated error.

[0052] (Data correction example 7) In the specific processing, if there is a tendency for the difference between the positioning imaging data and the main imaging data to be large, the data correction unit 4b may correct the main imaging data by multiplying the main imaging data by a coefficient corresponding to the ratio between the positioning imaging data and the main imaging data. A case where there is a tendency for the difference between the imaging data to be large may be interpreted as a case where the amount of X-rays detected by the X-ray detector 15 is at a level where it is affected by pile-up, that is, at a level where errors may occur in the imaging data. In the example described above, the coefficient corresponding to the ratio between the positioning imaging data and the main imaging data may be interpreted as the ratio of the number of X-ray photons.

[0053] (Data correction example 8) In the specific processing, the data corrector 4b may correct the main imaging data by multiplying the main imaging data by a coefficient corresponding to the ratio between the positioning imaging data, which tends to have a low projection value during scanning, and the main imaging data. During scanning (low-dose imaging), the amount of X-rays passing through the subject 6 varies depending on the type of part (heart, bone, etc.) of the subject 6. If the number of X-ray photons detected by the detector (X-ray detector 15) is large, the projection value will be low and the subject will be susceptible to pile-up. Therefore, the data corrector 4b may use imaging data that is susceptible to pile-up, i.e., positioning imaging data, which has a low projection value during low-dose imaging, and multiply the main imaging data by a coefficient corresponding to the ratio between the data and the main imaging data.

[0054] (Data correction example 9) In the identification process, the data corrector 4b may correct the main imaging data so that a specific representative value of the positioning imaging data and the main imaging data is equal for both the positioning imaging data and the main imaging data. The representative value may be interpreted as, for example, an average value of the imaging data for a specific frequency component (e.g., a low frequency component) contained in the imaging data and its surrounding components (medium-high frequency components).

[0055] (Data correction example 10) In the specific processing, the data corrector 4b may correct the main scan data by mixing the low-frequency components contained in the positioning scan data with the high-frequency components contained in the main scan data. Mixing the low-frequency components contained in the positioning scan data with the high-frequency components contained in the main scan data may be interpreted as combining the low-frequency components of the low-dose scan data, which are less susceptible to pile-up, with the high-frequency components of the high-dose scan data, which are less susceptible to noise depending on the X-ray dose. The positioning scan data has high-frequency errors, and the main scan data has low-frequency errors. Therefore, the data corrector 4b improves the correction accuracy of the main scan data by using the low-frequency components of the positioning scan data and the high-frequency components of the main scan data.

[0056] (Data correction example 11) In the identification process, the data corrector 4b may compare the low-frequency components contained in the positioning imaging data and the main imaging data, and based on the comparison result, correct the main imaging data so that the low-frequency components contained in the main imaging data become closer to the low-frequency components contained in the positioning imaging data. Specifically, the data corrector 4b may utilize the fact that the positioning imaging data and the main imaging data have similar correction amounts if the data have similar projection values, and may compare, for example, the low-frequency components during low-dose imaging with the low-frequency components during high-dose imaging, and correct the main imaging data so that the low-frequency components during high-dose imaging become closer to the low-frequency components during low-dose imaging.

[0057] (Data correction example 12) In the specific processing, the data corrector 4b may reconstruct a tomographic image of the subject 6 by blending the positioning imaging data and the corrected main imaging data. Specifically, the low-frequency information of the positioning imaging data is mixed with the high-frequency information of the main imaging data. More specifically, since noise is high-frequency information, the main imaging data acquired at a high dose is used, and since errors such as pile-up are relatively low-frequency information, the low-frequency information of the positioning imaging data with less errors such as pile-up is used for blending. By reconstructing a tomographic image in this manner, it is possible to obtain a tomographic image with good image quality. Note that the data to be corrected may include normal image data, spectral data (basis material data, virtual monochromatic data, energy-discriminated data (material-discriminated image data)), etc.

[0058] (Data output section 4c) The data output section 4c may output the data corrected by the data correcting section 4b, that is, the corrected photographic data.

[0059] Next, the operation of the medical diagnostic device 4 will be described with reference to Fig. 4. Fig. 4 is a flowchart for explaining the operation of the medical diagnostic device 4.

[0060] In step S1, the data acquisition unit 4a may acquire positioning imaging data obtained by scanning the subject 6 with a first dose before the main imaging of the subject 6, and main imaging data obtained by performing the main imaging of the subject 6 with a second dose higher than the first dose. In step S2, the data correction unit 4b may correct the main imaging data by a specific process using at least the positioning imaging data. In step S3, the data output unit 4c may output the data corrected by the data correction unit 4b, i.e., the corrected imaging data.

[0061] As described above, the medical diagnostic apparatus 4 of the present disclosure acquires positioning imaging data obtained by scanning the subject 6 at a first dose before the actual imaging of the subject 6, and actual imaging data obtained by performing the actual imaging of the subject 6 at a second dose higher than the first dose, corrects the actual imaging data by a specific process using at least the positioning imaging data, and outputs the corrected imaging data.

[0062] According to the medical diagnostic device 4 of the present disclosure, even if the count of the number of times radiation is detected and the energy of the incident radiation are misjudged during the main scan, the high-dose imaging data can be corrected by using low-dose imaging data that is less susceptible to pile-up, thereby reducing errors contained in the imaging data.

[0063] In the above embodiment, the following various processors can be used as the hardware structure of the processing units that perform various processes, such as the data acquisition unit 4a, the data correction unit 4b, and the data output unit 4c. As described above, the various processors include a CPU, which is a general-purpose processor that executes software (programs) and functions as various processing units, as well as dedicated electrical circuits that are processors having a circuit configuration specifically designed to perform specific processes, such as a programmable logic device (PLD), a processor whose circuit configuration can be changed after manufacture, such as an FPGA (Field-Programmable Gate Array), a graphics processing unit (GPU), and an application-specific integrated circuit (ASIC).

[0064] A single processing unit may be configured with one of these various processors, or may be configured with a combination of two or more processors of the same or different types (for example, a combination of multiple FPGAs, or a combination of a CPU and an FPGA). Also, multiple processing units may be configured with a single processor.

[0065] Examples of configuring multiple processing units with a single processor include, first, a form in which one processor is configured with a combination of one or more CPUs and software, and this processor functions as multiple processing units, as typified by computers such as client and server. Second, a form in which a processor is used to realize the functions of the entire system including multiple processing units with a single IC (Integrated Circuit) chip, as typified by systems on chips (SoCs). In this way, various processing units are configured using one or more of the above-mentioned various processors as a hardware structure.

[0066] Furthermore, more specifically, the hardware structure of these various processors can be an electric circuit that combines circuit elements such as semiconductor elements.

[0067] In the above embodiment, the data control program 42 is pre-stored (installed) in the memory 46, but this is not limiting. The data control program 42 may be provided in a form recorded on a recording medium such as a CD-ROM (Compact Disc Read Only Memory), a DVD-ROM (Digital Versatile Disc Read Only Memory), or a USB (Universal Serial Bus) memory. The data control program 42 may also be downloaded from an external device via a network.

[0068] In addition to the data control program 42, the technology of the present disclosure also extends to a computer-readable storage medium (such as a CD-ROM, DVD-ROM, or USB memory) that non-temporarily stores the data control program 42.

[0069] Furthermore, the present disclosure is not limited to the above, and it goes without saying that various modifications can be made without departing from the spirit of the present disclosure. The present invention can also be applied to a program product.

[0070] The following additional notes are provided regarding the above-described embodiments. (Appendix 1) 1. A medical diagnostic device comprising at least one processor, The processor: acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; correcting the main photography data through a specification process using at least the positioning photography data, and outputting the corrected photography data; Medical diagnostic equipment. (Appendix 2) 2. The medical diagnostic apparatus according to claim 1, wherein the processor acquires, as the main imaging data, data obtained by synchronizing the imaging trajectory during the main imaging with the imaging trajectory during the scan. (Appendix 3) 3. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identification process, generates forward projection data of the positioning shooting data by forward projecting a positioning image included in the acquired positioning shooting data in accordance with the trajectory of the actual shooting data, and corrects the actual shooting data using the generated forward projection data. (Appendix 4) 4. The medical diagnostic apparatus according to claim 1, wherein the processor corrects the actual shooting data using a difference between the positioning shooting data and the actual shooting data in the identification process. (Appendix 5) 5. The medical diagnostic apparatus according to claim 1, wherein the processor corrects the actual imaging data in the identification process by using a difference between the positioning imaging data and the actual imaging data in a portion of the imaging data other than high-frequency noise contained therein. (Appendix 6) 6. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identification process, corrects the actual photographing data by using a difference between the positioning photographing data and the actual photographing data from which high-frequency noise contained in each of the positioning photographing data and the actual photographing data has been removed. (Appendix 7) 7. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identification process, corrects the actual shooting data using a difference between a portion of the positioning shooting data from which noise has been removed and the actual shooting data. (Appendix 8) 8. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identifying process, estimates the magnitude of an error during the actual imaging based on the number of photons or projection values ​​detected by a detector, and corrects the actual imaging data using the positioning imaging data so as to remove the estimated error. (Appendix 9) The medical diagnostic device of any one of appendices 1 to 8, wherein, in the specific processing, if there tends to be a large difference between the positioning shooting data and the actual shooting data, the processor corrects the actual shooting data by multiplying the actual shooting data by a coefficient corresponding to the ratio between the positioning shooting data and the actual shooting data. (Appendix 10) 11. The medical diagnostic apparatus according to claim 1, wherein the processor corrects the actual imaging data by multiplying the actual imaging data by a coefficient corresponding to a ratio between the positioning imaging data, which tends to have a low projection value during scanning, and the actual imaging data, in the specific processing. (Appendix 11) The medical diagnostic apparatus of claim 10, wherein the processor, in the identification process, corrects the actual imaging data so that specific representative values ​​of the positioning imaging data and the actual imaging data are equal in both the positioning imaging data and the actual imaging data. (Appendix 12) 12. The medical diagnostic apparatus of claim 1, wherein the processor corrects the actual imaging data by mixing low-frequency components contained in the positioning imaging data with high-frequency components contained in the actual imaging data in the identification process. (Appendix 13) 13. The medical diagnostic apparatus of claim 1, wherein the processor, in the identification process, compares the low-frequency components contained in the positioning shooting data and the main shooting data, and corrects the main shooting data based on the comparison result so that the low-frequency components contained in the main shooting data are closer to the low-frequency components contained in the positioning shooting data. (Appendix 14) 14. The medical diagnostic apparatus of claim 1, wherein the processor, in the specific processing, reconstructs a tomographic image of the subject by blending the positioning imaging data and the corrected main imaging data. (Appendix 15) acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; The main photographing data is corrected by a specific process using at least the positioning photographing data, and the corrected photographing data is output. A data control method implemented by a computer. (Appendix 16) acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; The main photographing data is corrected by a specific process using at least the positioning photographing data, and the corrected photographing data is output. A data control program that causes a computer to execute a task. (Appendix 17) At least one processor acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; correcting the main photography data through a specification process using at least the positioning photography data, and outputting the corrected photography data; A computer program product including a program for causing a process to be performed, including [Explanation of symbols]

[0071] 1. Scanner 3 berths 4 Medical diagnostic equipment 4a Data acquisition section 4b Data correction section 4c Data output section 6. Subjects 11 Mounting stand 12 Rotating Plate 13 X-ray tube equipment 14 Collimator 15 X-ray detector 16 Data Collection Equipment 17 Rotating plate drive unit 18 Collimator control device 19 Rotating plate drive control device 20 X-ray high voltage generator 21 Data transmission equipment 31 Top plate 32 Bed control device 33 Tabletop up / down movement control device 34 Top plate forward / backward movement control device 42 Data Control Program 43 Storage section 44 Display 45 Input Devices 46 memory 48 Bus 100 Medical Diagnostic Systems

Claims

1. 1. A medical diagnostic device comprising at least one processor, The processor: acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; correcting the main photography data through a specification process using at least the positioning photography data, and outputting the corrected photography data; Medical diagnostic equipment.

2. The medical diagnostic apparatus according to claim 1 , wherein the processor acquires, as the main imaging data, data obtained by synchronizing an imaging trajectory during the main imaging with an imaging trajectory during the scan.

3. 2. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identification process, generates forward projection data of the positioning imaging data by forward projecting a positioning image included in the acquired positioning imaging data in accordance with a trajectory of the actual imaging data, and corrects the actual imaging data using the generated forward projection data.

4. The medical diagnostic apparatus according to claim 1 , wherein the processor corrects the main imaging data by using a difference between the positioning imaging data and the main imaging data in the specifying process.

5. The medical diagnostic apparatus according to claim 1 , wherein the processor corrects the main imaging data in the specifying process by using a difference between the positioning imaging data and the main imaging data in an imaging data portion other than high frequency noise contained therein.

6. 2. The medical diagnostic apparatus according to claim 1, wherein the processor, in the specification process, corrects the main imaging data using a difference between imaging data portions from which high frequency noise contained in the positioning imaging data and the main imaging data has been removed.

7. The medical diagnostic apparatus according to claim 1 , wherein the processor corrects the main imaging data in the specifying process by using a difference between a portion of the positioning imaging data from which noise has been removed and the main imaging data.

8. 2. The medical diagnostic apparatus according to claim 1, wherein the processor, in the identification process, estimates a magnitude of an error during the actual imaging based on the number of photons or the projection value detected by a detector, and corrects the actual imaging data using the positioning imaging data so as to remove the estimated error.

9. 2. The medical diagnostic device of claim 1, wherein, in the identification process, if there is a tendency for the difference between the positioning shooting data and the actual shooting data to be large, the processor corrects the actual shooting data by multiplying the actual shooting data by a coefficient corresponding to the ratio between the positioning shooting data and the actual shooting data.

10. 2. The medical diagnostic apparatus according to claim 1, wherein the processor corrects the actual imaging data by multiplying the actual imaging data by a coefficient corresponding to a ratio between the positioning imaging data, which tends to have a low projection value during the scan, and the actual imaging data, in the identification process.

11. The medical diagnostic apparatus according to claim 10, wherein the processor, in the identification process, corrects the main imaging data so that specific representative values ​​of the positioning imaging data and the main imaging data are equal in both the positioning imaging data and the main imaging data.

12. The medical diagnostic apparatus according to claim 1 , wherein the processor corrects the main scanning data by mixing a low frequency component included in the positioning scanning data with a high frequency component included in the main scanning data in the specifying process.

13. 2. The medical diagnostic apparatus of claim 1, wherein the processor, in the identification process, compares the low-frequency components contained in the positioning shooting data and the main shooting data, and corrects the main shooting data based on the comparison result so that the low-frequency components contained in the main shooting data are closer to the low-frequency components contained in the positioning shooting data.

14. The medical diagnostic apparatus according to claim 1 , wherein the processor, in the specifying process, reconstructs a tomographic image of the subject by blending the positioning imaging data and the corrected main imaging data.

15. acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; The main photographing data is corrected by a specific process using at least the positioning photographing data, and the corrected photographing data is output. A data control method implemented by a computer.

16. acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; The main photographing data is corrected by a specific process using at least the positioning photographing data, and the corrected photographing data is output. A data control program that causes a computer to execute a task.

17. At least one processor acquiring positioning imaging data obtained by scanning the subject at a first dose before the main imaging of the subject, and main imaging data obtained by performing the main imaging of the subject at a second dose higher than the first dose; correcting the main photography data through a specification process using at least the positioning photography data, and outputting the corrected photography data; A computer program product including a program for causing a process to be performed, including

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