JP2020203191A - Dynamic analysis system and program - Google Patents

Abstract

To easily grasp a difference between dynamic images to be compared.SOLUTION: According to a diagnosis console 3, a control unit 31 acquires a cycle of a time change in a feature amount related to a function of a diagnosis object from each of a plurality of dynamic images, adjusts the acquired cycle, and generates a plurality of pieces of cycle adjusted data in which the cycles of the time change in the feature amount are equal. The control unit then generates difference information for each of the same phase of the plurality of pieces of cycle adjusted data, and causes a display part 34 to display the same.SELECTED DRAWING: Figure 3

Description

The present invention relates to dynamic analysis systems and programs.

When the dynamic images obtained by photographing the dynamics of the subject with periodicity are comparatively interpreted, the dynamics cycle differs between the dynamic images. Therefore, there is a problem that appropriate comparative evaluation cannot be performed.

Therefore, for example, Patent Document 1 describes a technique for displaying periodic changes of two images in a specific phase for each period of a reference moving image to be compared with a reference moving image.

International release WO2014 / 054379

However, as described in Patent Document 1, there is a problem that it is difficult to intuitively understand the difference only by aligning the periods of a plurality of dynamic images and displaying them synchronously.

An object of the present invention is to make it easy to grasp the difference between the dynamic images to be compared.

In order to solve the above problems, the dynamic image analysis system of the invention according to claim 1 is used.
A graph showing the time change of the feature amount related to the function of the diagnosis target is generated from each of the plurality of dynamic images obtained by radiographing the dynamics of the living body, and the time change of the feature amount is based on the generated graph. Cycle acquisition means to acquire the cycle and
By adjusting at least one period of the graph showing the time change of the feature amount generated from the plurality of dynamic images, a plurality of periods of the feature amount with the same time change period are used as the plurality of period adjustment data. Period adjustment data generation means to generate graphs,
A difference information generating means for generating difference information for each of the same phases of the plurality of period adjustment data, and
An output means for outputting the difference information and
To be equipped.

The invention according to claim 2 is the invention according to claim 1.
The cycle adjustment data generation means generates the plurality of cycle adjustment data in which the phases of the start timings match.
The difference information generating means calculates the difference value of the feature amount at the same timing in the plurality of cycle adjustment data.

The dynamic analysis system of the invention according to claim 3 is
The first dynamic image obtained by radiographing the dynamics of the living body is analyzed to generate the first analysis result image, and the second dynamic image obtained by radiographing the dynamics of the living body is obtained. An analysis means that analyzes and generates a second analysis result image,
A difference information generation means for generating difference information for each phase of the first analysis result image and the second analysis result image, and
An output means for outputting the difference information and
To be equipped.

The invention according to claim 4 is the invention according to claim 3.
From the first analysis result image, the time change cycle of the first feature amount related to the function to be diagnosed, and from the second analysis result image, the time change of the second feature amount related to the function to be diagnosed. Cycle acquisition means to acquire the cycle and
The first analysis result image and the first analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other by adjusting the cycle acquired by the cycle acquisition means. Period adjustment data generation means for generating the second analysis result image,
To be equipped.

The invention according to claim 5 is the invention according to claim 4.
The period adjustment data generation means adds or deletes a frame image to at least one of the first analysis result image and the second analysis result image, so that the period of time change of the first feature amount can be obtained. The first analysis result image and the second analysis result image having the same period of time change of the second feature amount are generated.

The invention according to claim 6 is the invention according to claim 5.
The period adjustment data generation means adds a signal value of each pixel in a frame image to be added to at least one of the first analysis result image and the second analysis result image to a plurality of frames of the added analysis result image. It is calculated by interpolating using the signal values of the pixels at the same position in the image.

The invention according to claim 7 is the invention according to claim 4.
The period adjustment data generation means generates an interpolated image based on signal values of a plurality of frame images selected from at least one of the first analysis result image and the second analysis result image. The first analysis result image and the second analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal are generated.

The invention according to claim 8 is the invention according to any one of claims 5 to 7.
The period adjustment data generation means generates the first analysis result image and the second analysis result image in which the phases of the start timings match.
The difference information generating means calculates the difference value of the signal values of the pixels of the same coordinates of the frame image at the same timing in the first analysis result image and the second analysis result image.

The invention according to claim 9 is the invention according to claim 4.
The cycle acquisition means has a graph showing a time change of the feature amount related to the function of the diagnosis target from the first analysis result image, and a time of the feature amount related to the function of the diagnosis target from the second analysis result image. A graph showing the change is generated, and the time change cycle of the first feature amount and the time change cycle of the second feature amount are acquired based on the generated graph.
The period adjustment data generating means includes a graph showing a time change of the first feature amount generated from the first analysis result image and a time of the second feature amount generated from the second analysis result image. By adjusting at least one cycle with the graph showing the change, a plurality of graphs in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal are generated.

The invention according to claim 10 is the invention according to claim 9.
The period adjustment data generation means generates the first analysis result image and the second analysis result image in which the phases of the start timings match.
The difference information generating means calculates the difference value of the signal values at the same timing between the first analysis result image and the second analysis result image.

The invention according to claim 11 is the invention according to any one of claims 3 to 10.
The first dynamic image and the second dynamic image are dynamic images of the chest.

The invention according to claim 12 is the invention according to any one of claims 4 to 10.
The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the blood flow function or the ventilation function of the lung field.
The first feature amount and the second feature amount are signal values of pixels in the region of interest.

The invention according to claim 13 is the invention according to any one of claims 4 to 10.
The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the function of the diaphragm.
The first feature amount and the second feature amount are diaphragm positions.

The invention according to claim 14 is the invention according to any one of claims 3 to 13.
The output means synthesizes and outputs the difference information with at least one of the first analysis result image and the second analysis result image.

The program of the invention according to claim 15
Computer,
The first dynamic image obtained by radiographing the dynamics of the living body is analyzed to generate the first analysis result image, and the second dynamic image obtained by radiographing the dynamics of the living body is obtained. An analysis means that analyzes and generates a second analysis result image,
A difference information generation means for generating difference information for each phase of the first analysis result image and the second analysis result image.
An output means for outputting the difference information,
To function as.

The invention according to claim 16 is the invention according to claim 15.
The computer,
From the first analysis result image, the time change cycle of the first feature amount related to the function to be diagnosed, and from the second analysis result image, the time change of the second feature amount related to the function to be diagnosed. Cycle acquisition means to acquire the cycle and
The first analysis result image and the first analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other by adjusting the cycle acquired by the cycle acquisition means. Periodic adjustment data generation means for generating the second analysis result image,
To function as.

The invention according to claim 17 is the invention according to claim 15 or 16.
The first dynamic image and the second dynamic image are dynamic images of the chest.

The invention according to claim 18 is the invention according to claim 16.
The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the blood flow function or the ventilation function of the lung field.
The first feature amount and the second feature amount are signal values of pixels in the region of interest.

The invention according to claim 19 is the invention according to claim 16.
The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the function of the diaphragm.
The first feature amount and the second feature amount are diaphragm positions.

The invention according to claim 20 is the invention according to any one of claims 15 to 19.
The output means synthesizes and outputs the difference information with at least one of the first analysis result image and the second analysis result image.

According to the present invention, it is possible to easily grasp the difference between the dynamic images to be compared.

It is a figure which shows the whole structure of the dynamic analysis system in embodiment of this invention. It is a flowchart which shows the shooting control processing executed by the control part of the shooting console of FIG. FIG. 5 is a flowchart showing a difference display process A executed by the control unit of the diagnostic console of FIG. 1 in the first embodiment. It is a figure for demonstrating the adjustment of a period. It is a figure which shows the difference image displayed in step S16 of FIG. FIG. 5 is a flowchart showing a difference display process B executed by the control unit of the diagnostic console of FIG. 1 in the second embodiment. It is a figure which shows the difference graph displayed in step S25 of FIG. FIG. 5 is a flowchart showing a difference display process C executed by the control unit of the diagnostic console of FIG. 1 in the third embodiment. It is a figure which shows the difference image displayed in step S36 of FIG.

Hereinafter, embodiments of the present invention will be described with reference to the drawings. However, the scope of the invention is not limited to the illustrated examples.

<First Embodiment>
[Configuration of dynamic analysis system 100]
First, the configuration of the first embodiment will be described.
FIG. 1 shows the overall configuration of the dynamic analysis system 100 according to the first embodiment.
As shown in FIG. 1, in the dynamic analysis system 100, the imaging device 1 and the imaging console 2 are connected by a communication cable or the like, and the imaging console 2 and the diagnostic console 3 are connected to a LAN (Local Area Network) or the like. It is configured to be connected via the communication network NT of. Each device constituting the dynamic analysis system 100 conforms to the DICOM (Digital Image and Communications in Medicine) standard, and communication between the devices is performed according to DICOM.

[Structure of imaging device 1]
The imaging device 1 is an imaging means that photographs dynamics having a periodicity (cycle), such as morphological changes in lung expansion and contraction associated with respiratory movements, and heart beating. In dynamic photography, radiation such as X-rays is pulsed and repeatedly irradiated at predetermined time intervals (pulse irradiation), or low dose rate is continuously irradiated (continuous irradiation). By doing so, it means to acquire a plurality of images showing the dynamics of the subject. A series of images obtained by dynamic photography is called a dynamic image. Further, each of the plurality of images constituting the dynamic image is called a frame image. In the following embodiment, a case where dynamic imaging of the chest is performed by pulse irradiation will be described as an example.

The radiation source 11 is arranged at a position facing the radiation detection unit 13 with the subject M (subject) in between, and irradiates the subject M with radiation (X-rays) under the control of the radiation irradiation control device 12.
The radiation irradiation control device 12 is connected to the imaging console 2, and controls the radiation source 11 based on the irradiation conditions input from the imaging console 2 to perform radiation imaging. Irradiation conditions input from the shooting console 2 include, for example, pulse rate, pulse width, pulse interval, number of shooting frames per shooting, X-ray tube current value, X-ray tube voltage value, additional filter type, etc. Is. The pulse rate is the number of irradiations per second, which is consistent with the frame rate described later. The pulse width is the irradiation time per irradiation. The pulse interval is the time from the start of one irradiation to the start of the next irradiation, and is consistent with the frame interval described later.

The radiation detection unit 13 is composed of a semiconductor image sensor such as an FPD. The FPD has, for example, a glass substrate or the like, detects radiation emitted from a radiation source 11 at a predetermined position on the substrate and transmitted at least through the subject M according to its intensity, and detects the detected radiation as an electric signal. A plurality of detection elements (pixels) that are converted into and accumulated in a matrix are arranged in a matrix. Each pixel is configured to include a switching unit such as a TFT (Thin Film Transistor). The FPD has an indirect conversion type that converts X-rays into an electric signal by a photoelectric conversion element via a scintillator and a direct conversion type that directly converts X-rays into an electric signal, and either of them may be used.
The radiation detection unit 13 is provided so as to face the radiation source 11 with the subject M interposed therebetween.

The reading control device 14 is connected to the photographing console 2. The reading control device 14 controls the switching unit of each pixel of the radiation detection unit 13 based on the image reading condition input from the photographing console 2 to switch the reading of the electric signal stored in each pixel. Then, the image data is acquired by reading the electric signal stored in the radiation detection unit 13. This image data is a frame image. Then, the reading control device 14 outputs the acquired frame image to the shooting console 2. The image reading conditions are, for example, a frame rate, a frame interval, a pixel size, an image size (matrix size), and the like. The frame rate is the number of frame images acquired per second, which is consistent with the pulse rate. The frame interval is the time from the start of one frame image acquisition operation to the start of the next frame image acquisition operation, and is consistent with the pulse interval.

Here, the radiation irradiation control device 12 and the reading control device 14 are connected to each other and exchange synchronization signals with each other to synchronize the radiation irradiation operation and the image reading operation.

[Configuration of shooting console 2]
The imaging console 2 outputs radiation irradiation conditions and image reading conditions to the imaging device 1 to control radiation imaging and radiation image reading operations by the imaging device 1, and a camera operator captures a dynamic image acquired by the imaging device 1. It is displayed for confirmation of positioning by the photographer and confirmation of whether or not the image is suitable for diagnosis.
As shown in FIG. 1, the photographing console 2 includes a control unit 21, a storage unit 22, an operation unit 23, a display unit 24, and a communication unit 25, and each unit is connected by a bus 26.

The control unit 21 is composed of a CPU (Central Processing Unit), a RAM (Random Access Memory), and the like. The CPU of the control unit 21 reads out the system program and various processing programs stored in the storage unit 22 and expands them in the RAM in response to the operation of the operation unit 23, and performs the shooting control processing described later according to the expanded program. Various processes including the above are executed to centrally control the operation of each part of the photographing console 2 and the irradiation operation and reading operation of the photographing device 1.

The storage unit 22 is composed of a non-volatile semiconductor memory, a hard disk, or the like. The storage unit 22 stores data such as parameters or processing results necessary for executing processing by various programs and programs executed by the control unit 21. For example, the storage unit 22 stores a program for executing the photographing control process shown in FIG. In addition, the storage unit 22 stores the irradiation condition and the image reading condition in association with the inspection target site (here, the chest). Various programs are stored in the form of readable program code, and the control unit 21 sequentially executes operations according to the program code.

The operation unit 23 is configured to include a keyboard equipped with cursor keys, number input keys, various function keys, and a pointing device such as a mouse, and controls an instruction signal input by key operation on the keyboard or mouse operation. Output to 21. Further, the operation unit 23 may include a touch panel on the display screen of the display unit 24, and in this case, the operation unit 23 outputs an instruction signal input via the touch panel to the control unit 21.

The display unit 24 is composed of a monitor such as an LCD (Liquid Crystal Display) or a CRT (Cathode Ray Tube), and displays input instructions, data, and the like from the operation unit 23 according to instructions of display signals input from the control unit 21. To do.

The communication unit 25 includes a LAN adapter, a modem, a TA (Terminal Adapter), and the like, and controls data transmission / reception with each device connected to the communication network NT.

[Configuration of diagnostic console 3]
The diagnostic console 3 is a device for acquiring a dynamic image from the imaging console 2 and displaying the acquired dynamic image and the analysis result of the dynamic image to support the diagnosis of a doctor.
As shown in FIG. 1, the diagnostic console 3 includes a control unit 31, a storage unit 32, an operation unit 33, a display unit 34, and a communication unit 35, and each unit is connected by a bus 36.

The control unit 31 is composed of a CPU, RAM, and the like. The CPU of the control unit 31 reads out the system program and various processing programs stored in the storage unit 32 and expands them in the RAM in response to the operation of the operation unit 33, and according to the expanded program, the difference image described later. Various processes such as display process A are executed to centrally control the operation of each part of the diagnostic console 3. The control unit 31 functions as a cycle acquisition means, a cycle adjustment data generation means, a difference information generation means, and a lung field information transformation means.

The storage unit 32 is composed of a non-volatile semiconductor memory, a hard disk, or the like. The storage unit 32 stores data such as various programs including a program for executing the difference image display processing A in the control unit 31, parameters necessary for executing the processing by the program, or processing results. These various programs are stored in the form of a readable program code, and the control unit 31 sequentially executes an operation according to the program code.

Further, in the storage unit 32, dynamic images taken in the past include patient information (for example, patient ID, patient's name, height, weight, age, gender, etc.) and examination information (for example, examination ID, examination date, examination). It is stored in association with the target site (here, the chest) and the type of function of the diagnosis target (for example, ventilation, blood flow, diaphragm), etc.

The operation unit 33 is configured to include a keyboard equipped with cursor keys, number input keys, various function keys, etc., and a pointing device such as a mouse, and receives an instruction signal input by a user's key operation on the keyboard or mouse operation. Output to the control unit 31. Further, the operation unit 33 may include a touch panel on the display screen of the display unit 34, and in this case, the operation unit 33 outputs an instruction signal input via the touch panel to the control unit 31.

The display unit 34 is composed of a monitor such as an LCD or a CRT, and performs various displays according to an instruction of a display signal input from the control unit 31. The display unit 34 functions as an output means.

The communication unit 35 includes a LAN adapter, a modem, a TA, and the like, and controls data transmission / reception with each device connected to the communication network NT.

[Operation of dynamic analysis system 100]
Next, the operation of the dynamic analysis system 100 in this embodiment will be described.

(Operation of shooting device 1 and shooting console 2)
First, a shooting operation by the shooting device 1 and the shooting console 2 will be described.
FIG. 2 shows a shooting control process executed by the control unit 21 of the shooting console 2. The photographing control process is executed in collaboration with the control unit 21 and the program stored in the storage unit 22.

First, the photographer operates the operation unit 23 of the imaging console 2 to input patient information and examination information of the subject (subject M) (step S1).

Next, the radiation irradiation condition is read from the storage unit 22 and set in the radiation irradiation control device 12, and the image reading condition is read from the storage unit 22 and set in the reading control device 14 (step S2).

Next, the instruction of radiation irradiation by the operation of the operation unit 23 is waited for (step S3). Here, the photographer arranges the subject M between the radiation source 11 and the radiation detection unit 13 for positioning. In addition, the subject (subject M) is instructed on the respiratory state. For example, the subject (subject M) is instructed to relax and encourages resting breathing. If the type of function to be diagnosed is ventilation, rest breathing may be promoted, and if the type of function to be diagnosed is blood flow, the subject may be instructed to hold his / her breath. When the shooting preparation is completed, the operation unit 23 is operated to input the irradiation instruction.

When the irradiation instruction is input by the operation unit 23 (step S3; YES), the imaging start instruction is output to the radiation irradiation control device 12 and the reading control device 14, and the dynamic imaging is started (step S4). That is, radiation is irradiated by the radiation source 11 at the pulse interval set in the radiation irradiation control device 12, and a frame image is acquired by the radiation detection unit 13.

When the imaging of a predetermined number of frames is completed, the control unit 21 outputs an instruction to end the imaging to the radiation irradiation control device 12 and the reading control device 14, and the imaging operation is stopped. The number of frames captured is the number of frames that can be captured in at least one breathing cycle.

The frame images acquired by shooting are sequentially input to the shooting console 2, stored in the storage unit 22 in association with a number indicating the shooting order (frame number) (step S5), and displayed on the display unit 24. (Step S6). The photographer confirms the positioning and the like from the displayed dynamic image, and determines whether the image suitable for the diagnosis is acquired by the image (shooting OK) or the re-shooting is necessary (shooting NG). Then, the operation unit 23 is operated to input the determination result.

When a determination result indicating that shooting is OK is input by a predetermined operation of the operation unit 23 (step S7; YES), an identification ID for identifying the dynamic image and each of the series of frame images acquired in the dynamic shooting are used. , Patient information, examination information, irradiation conditions, image reading conditions, numbers (frame numbers) indicating the imaging order, etc. are attached (for example, written in the header area of image data in DICOM format), and the communication unit 25 is It is transmitted to the diagnostic console 3 via (step S8). Then, this process ends. On the other hand, when a determination result indicating shooting NG is input by a predetermined operation of the operation unit 23 (step S7; NO), a series of frame images stored in the storage unit 22 is deleted (step S9), and this process is performed. finish. In this case, re-shooting is required.

(Operation of diagnostic console 3)
Next, the operation in the diagnostic console 3 will be described.
In the diagnostic console 3, when a series of frame images of dynamic images of ventilation or blood flow for the function to be diagnosed are received from the imaging console 2 via the communication unit 35, they are stored in the control unit 31 and the storage unit 32. The difference display process A shown in FIG. 3 is executed in cooperation with the program.

Hereinafter, the flow of the difference display process A will be described with reference to FIG.
First, a past dynamic image to be compared with the received dynamic image is selected (step S10).
In step S10, for example, a list of past dynamic images of the subject M stored in the storage unit 32 is displayed on the display unit 34, and the dynamic image desired by the user is selected from the displayed dynamic images by the operation unit 33. Of the past dynamic images of the subject M stored in the storage unit 32, the control unit 31 may automatically select the dynamic image having the latest inspection date. The received dynamic image is referred to as a current dynamic image, and the dynamic image comparing with the current dynamic image is referred to as a past dynamic image.

Next, the current dynamic image and the past dynamic image are subjected to warping processing to match the shapes of the lung field regions (step S11).
For example, in step S11, first, the contour of the lung field region is detected from each of the frame image constituting the current dynamic image and the frame image constituting the past dynamic image. For example, in each frame image, a threshold value is obtained by discriminant analysis from a histogram of the signal value (density value) of each pixel, and a region having a signal higher than this threshold value is primarily extracted as a lung field region candidate. The boundary of the lung field region can be extracted by performing edge detection near the boundary of the primary extracted lung field region candidate and extracting the point where the edge is maximum in the small region near the boundary along the boundary. Next, one frame image is selected from all the frame images of the current dynamic image and the past dynamic image and used as the reference image, so that the lung field shape of the other frame images matches the lung field shape of the reference image. Is warped. The reference image may be a frame image of the first frame of the current dynamic image or the past dynamic image, or may be a frame image of the maximum expiratory position or the maximum inspiratory position. Alternatively, an image of the reference lung field shape may be prepared in advance, and the lung field shape of both dynamic images may be matched with the reference lung field shape. As a result, the shape of the lung field when comparing dynamic images is always unified, so that the user can perform comparative evaluation of dynamic images in the same environment.

Next, the feature amount (here, the signal value of ROI) related to the function to be diagnosed is calculated from the current dynamic image and the past dynamic image, and the cycle of the time change of the calculated feature amount is acquired (step S12). ).

In the ventilation function by respiration, when the lung field is expanded by inspiration, the density of the lung field region becomes low, so that the amount of X-ray transmission increases and the signal value (concentration value) of the lung field region on the dynamic image becomes high. When the lung field contracts due to exhalation, the density of the lung field region increases, so that the amount of X-ray transmission decreases, and the signal value of the lung field region on the dynamic image decreases. Therefore, when the function to be diagnosed is ventilation, the time change of the signal value in the dynamic image can be used as the feature amount related to the ventilation function. In addition, when blood flows into the lungs due to respiration, the amount of X-ray transmission in the blood flow portion decreases, and the signal value on the dynamic image becomes low. Therefore, when the function to be diagnosed is blood flow, the time change of the signal value in the dynamic image can be used as the feature amount related to the blood flow function.

For example, when the function to be diagnosed is ventilation, first, a low-pass filter process in the time direction is applied to the lung field region of both past and present dynamic images. Specifically, the time change of the signal value is obtained for each pixel of the dynamic image and filtered by a low-pass filter in the time direction (for example, a cutoff frequency of 0.80 Hz). As a result, the high frequency component due to blood flow or the like can be removed to obtain the ventilation signal component.
Next, an ROI (region of interest) is set for each frame image of the two dynamic images after the low-pass filter processing. Here, the position of the ROI is preferably set to a position where the characteristics of the function to be diagnosed are most apparent. If the function to be diagnosed is ventilation, the ROI is preferably set within the lung field region excluding the heart and spine. The ROI may be set automatically by image processing, or may be set (manually) according to the operation of the operation unit 33 by the user.
Next, in each of the current dynamic image and the past dynamic image, the representative value (for example, average value, median value, etc.) of the signal value of each pixel in the ROI of each frame image is calculated, and the calculated representative value is used as the time. By plotting in a series (in the order of frame images), a waveform graph (called a waveform graph) showing the time change of the signal value is generated.
Then, from the generated waveform graph, the period of time change of the signal value in each of the current dynamic image and the past dynamic image is acquired. The period can be calculated with the time from the maximum point (or minimum point) of the waveform graph to the next maximum point (or minimum point) as the period.

Further, for example, when the function to be diagnosed is blood flow, first, a high-pass filter process in the time direction is performed in the lung field region of both the past and present dynamic images. Specifically, the time change of the signal value is obtained for each pixel of the dynamic image and filtered by a high-pass filter in the time direction (for example, a cutoff frequency of 0.80 Hz). Filtering may be performed using a bandpass filter in the time direction (for example, a low-frequency cutoff frequency of 0.8 Hz and a high-frequency cutoff frequency of 2.4 Hz) on the time change of the signal value. As a result, the low frequency component due to ventilation or the like can be removed to obtain the signal component of the blood flow.
Next, the ROI is set for each frame image of the two dynamic images after the filtering. Here, the position of the ROI is preferably set to a position where the characteristics of the function to be diagnosed are most apparent. When the function to be diagnosed is blood flow, it is preferable to set the ROI in the cardiac region. The ROI may be set automatically by image processing, or may be set (manually) according to the operation of the operation unit 33 by the user.
Next, in each of the current dynamic image and the past dynamic image, the representative value (for example, average value, median value, etc.) of the signal value of each pixel in the ROI of each frame image is calculated, and the calculated representative value is used as the time. By plotting in a series (in order of frame number), a waveform graph (waveform graph) showing the time change of the signal value is generated.
Then, from the generated waveform graph, the period of time change of the signal value in each of the current dynamic image and the past dynamic image is acquired.

Next, the cycle is adjusted so that the cycle calculated from the current dynamic image and the cycle calculated from the past dynamic image match, and the cycle adjustment data is generated (step S13).
In step S13, as shown in FIG. 4, when the period acquired from the current dynamic image and the period acquired from the past dynamic image are different, the period is adjusted and two period adjustment data having the same period are generated. .. In the present embodiment, the cycle adjustment data is each of a plurality of dynamic images in which the cycles are matched (here, a current dynamic image and a past dynamic image in which the cycles are matched).

For example, first, the period of the adjusted dynamic image (the period of time change of the signal value; the same applies hereinafter) is determined. As the adjusted cycle, a short cycle may be matched with a long cycle, or a long cycle may be matched with a short cycle. Further, both cycles may be adjusted to a predetermined cycle.
Next, in order to match the cycle of each dynamic image with the adjusted cycle, the number of frame images to be added or deleted for each cycle in each dynamic image is determined. If the number of frame images to be added or deleted is 0, the process of adjusting the period of the dynamic image is not performed. Then, by adding or deleting a determined number of frame images for each period of the dynamic image that needs to be adjusted and matching the periods of the two dynamic images, two dynamic images having the same period, that is, Two cycle adjustment data are generated.

For example, when matching a short cycle to a long cycle, frame images are evenly added to the dynamic image of the shorter cycle to match the cycle. The signal value of each pixel of the frame image to be added is obtained by performing interpolation processing such as bilinear interpolation and bicubic interpolation using the signal values of the pixels at the same position in a plurality of frame images of the original dynamic image, for example. be able to. When adjusting the long cycle to the short cycle, the frame image is evenly thinned out (deleted) from the dynamic image of the longer cycle to match the cycle.

Alternatively, in a dynamic image that requires cycle adjustment, one or more frame images are selected for each cycle, and an interpolated image is generated based on the signal value of the selected frame image and the determined number of frame images. As the adjustment data, a plurality of dynamic images having the same period of time change of the signal value may be generated. For example, in a dynamic image in which the period needs to be adjusted, a waveform graph of the time change of the signal value is generated for each pixel corresponding between the frame images, the values of the maximum point and the minimum point are acquired, and the adjusted period. Period adjustment data by adjusting the number of frame images for each cycle by generating an interpolated image using bilinear interpolation, bicubic interpolation, etc., based on the number of frame images for each frame and the acquired signal values of the maximum and minimum points. May be generated. According to this method, the cycle can be adjusted even when the frame image cannot be added / deleted evenly (the frame image cannot be added / deleted evenly).

In addition, after adjusting the period, the amount of time shift of each period adjustment data for matching the phase of the start timing of the two period adjustment data with a predetermined phase (for example, the maximum point or the minimum point) is calculated. , The frame image of the periodic adjustment data is shifted in the time direction by the calculated shift amount. As a result, the phases of the start timings of the two period adjustment data can be matched.

Next, in the frame image of the same timing of the period adjustment data, the difference value of the signal value (for example, in the present embodiment, the signal value of the current period adjustment data to the signal of the past period adjustment data) for each pixel at the same coordinates. The value obtained by subtracting the value) is calculated (step S14), and the difference image is generated (step S15).
In step S15, for example, by superimposing a color corresponding to the calculated difference value (sign and absolute value) on each pixel of any of the periodic adjustment data (for example, the periodic adjustment data of the past dynamic image). Generate a difference image.

Then, the generated difference image is displayed on the display unit 34 (step S16), and the difference display process A ends.

FIG. 5 is a diagram showing two difference images at different timings displayed in step S16. As shown in FIG. 5, at the timing when the current signal value is increasing compared to the past, the color indicating that the signal value is increasing for each pixel depends on the magnitude of the absolute value of the difference value. It is displayed in the same concentration. At the timing when the current signal value is decreasing compared to the past, the color indicating that the density is decreasing is displayed in each pixel at the density corresponding to the magnitude of the absolute value of the difference value. Therefore, the user can easily grasp the difference in the function of the diagnosis target between the dynamic images to be compared.

<Modified example of the first embodiment>
In the first embodiment, the case where two dynamic images obtained by photographing the dynamics of the subject are compared has been described, but in the difference image display processing A, the dynamic images are pixel-by-pixel or a plurality of pixels. When comparing the analysis result images acquired by performing the dynamic analysis for each block (for example, the control unit 31 has a function of analyzing the dynamic image and generating the analysis result image, and analyzes the current dynamic image. It can also be applied (when comparing the analysis result image and the past analysis result image of the same patient stored in the storage unit 32). That is, by performing the same processing as in steps S11 to S16 of the difference display processing A on the two analysis result images to be compared, the difference can be visualized and easily grasped by the user.

However, in the warping process of step S11, warping is performed using the two dynamic images that are the sources of generating the two analysis result images. Specifically, the two dynamic images from which the two analysis result images were generated were subjected to warping processing so that the lung field shapes matched as described above, and the warping processing was performed on the two dynamic images. Coordinate transformation is also performed on the two analysis result images to match the lung field shapes in the analysis result images.

The analysis result image is an analysis of the function (ventilation and blood flow) of the diagnosis target for each pixel of the dynamic image or for each block of a plurality of pixels, and the signal value of each pixel is a feature amount related to the function of the diagnosis target. .. The specific method of analysis for obtaining the analysis result image is not limited, and for example, the following (1) to (3) can be used. In the following (1) to (3), the analysis is performed for each block (small area) of a plurality of pixels of the dynamic image, but it may be for each pixel.

(1) When the function to be diagnosed is blood flow, for example, the method described in JP2012-239996 can be used. That is, with respect to the pulsation signal waveform from the start of imaging, the pulsation signal waveform and the blood flow in each small region are shifted by one frame interval for each small region (while shifting in the time direction). The mutual correlation coefficient with the signal waveform is calculated, and a moving image in which the images showing the calculated mutual correlation coefficient in each small area are arranged as one frame for each frame shift is generated as a blood flow analysis result image. May be good.
The blood flow signal waveform is representative of the signal value of each pixel in the small region after high-pass filtering in the time direction (for example, low cutoff frequency 0.8 Hz) is applied to each small region of the series of frame images. It can be obtained by calculating a value (mean value, maximum value, etc.) and acquiring a waveform showing a time change of the calculated representative value.
Any of the following can be used as the pulsation signal waveform.
(A) A waveform in which an ROI (region of interest) is defined in the heart region (or aortic region) and showing a time change of a signal value in the ROI (b) A signal waveform obtained by reversing the waveform of (a) (c) Electrocardiographic detection Electrocardiographic signal waveform obtained from the sensor (d) Signal waveform indicating the movement (change in position) of the heart wall Further, the mutual correlation coefficient can be obtained by the following [Equation 1].

(2) When the function to be diagnosed is blood flow, as described in Japanese Patent Application Laid-Open No. 2013-81579, high-pass filter processing in the time direction (for example, low-frequency cutoff frequency 0.8 Hz) is performed for each small region. After applying, the difference value of the representative value (mean value, maximum value, etc.) of the signal value of each pixel in the small area is calculated between the adjacent frame images, and the calculated difference value between each adjacent frame image is calculated. A moving image in which the images shown in each small area are arranged in chronological order as one frame may be generated as a blood flow analysis result image. The inter-frame difference image generated by the above method has the signal change due to ventilation in each small region removed, and becomes an image showing the signal change due to blood flow in each small region.

(3) When the function to be diagnosed is ventilation, as described in Japanese Patent Application Laid-Open No. 2013-81579, low-pass filter processing in the time direction (for example, high-frequency cutoff frequency 0.8 Hz) is performed for each small region. After applying, the difference value of the representative value (mean value, maximum value, etc.) of the signal value of each pixel in the small area is calculated between the adjacent frame images, and the difference value calculated between each adjacent frame image is calculated. A moving image in which the images shown in the small area are arranged in chronological order as one frame may be generated as a ventilation analysis result image. The inter-frame difference image generated by the above method has the signal change due to blood flow in each small region removed, and becomes an image showing the signal change due to ventilation in each small region.

<Second embodiment>
Next, a second embodiment of the present invention will be described.
The configuration in the second embodiment is the same as that described in the first embodiment, except that the program for executing the difference display process B is stored in the storage unit 32 of the diagnostic console 3. The description will be omitted, and the operation of the second embodiment will be described below.

First, dynamic imaging is performed by the imaging device 1 and the imaging console 2, a dynamic image is generated, and a series of frame images of the dynamic image is transmitted from the imaging console 2 to the diagnostic console 3.

In the diagnostic console 3, when a series of frame images of dynamic images of ventilation or blood flow for the function to be diagnosed are received from the imaging console 2 via the communication unit 35, they are stored in the control unit 31 and the storage unit 32. The difference display process B shown in FIG. 6 is executed in cooperation with the program.
FIG. 6 is a flowchart showing the difference display process B executed by the diagnostic console 3 in the second embodiment. The difference display process B is executed in cooperation with the program stored in the control unit 31 and the storage unit 32.

Hereinafter, the flow of the difference display process B will be described with reference to FIG.
First, a past dynamic image to be compared with the received dynamic image is selected (step S20).
Since the process of step S20 is the same as the process of step S10 of FIG. 3, the description is incorporated.

Next, the feature amount (here, the signal value of ROI) related to the function to be diagnosed is calculated from the current dynamic image and the past dynamic image, and a waveform graph showing the time change of the calculated feature amount is generated. The cycle is acquired (step S21).
Since the process of step S21 is the same as the process of step S12 of FIG. 3, the description is incorporated. Each data plotted on the waveform graph is called signal value data.

Next, the period is adjusted so that the period of the waveform graph generated based on the current dynamic image and the period of the waveform graph generated based on the past dynamic image match, and the period adjustment data is generated (step S22). ).
In step S22, as shown in FIG. 4, when the period of the waveform graph generated based on the current dynamic image and the period of the waveform graph generated based on the past dynamic image are different, the period is adjusted and the period is adjusted. To unify. In the present embodiment, the period adjustment data is each of a plurality of waveform graphs in which the periods are combined.

For example, first, the period of the adjusted waveform graph (the period of time change of the signal value; the same applies hereinafter) is determined. As the adjusted cycle, a short cycle may be matched with a long cycle, or a long cycle may be matched with a short cycle. Further, both cycles may be adjusted to a predetermined cycle.
Next, in order to match the period of each waveform graph with the adjusted period, the number of signal value data to be added or deleted for each period in each waveform graph is determined. When the number of signal value data to be added or deleted is 0, the process of adjusting the period of the waveform graph is not performed. Then, by adding or deleting a determined number of signal value data for each period of the waveform graph that needs to be adjusted and matching the periods of the two waveform graphs, two waveform graphs having the same period, that is, 2 Two period adjustment data are generated.

For example, when adjusting the short period to the long period, the signal value data is evenly added to the waveform graph of the shorter period to adjust the period. The signal value data to be added can be obtained, for example, by performing interpolation processing such as bilinear interpolation and bicubic interpolation using the signal value data in the original waveform graph. When adjusting the long period to the short period, the signal value data is evenly thinned out (deleted) from the waveform graph of the longer period to adjust the period. The interval for plotting the signal value data in the waveform graph is the frame interval at the time of shooting.

Alternatively, in a waveform graph that requires a cycle change, select any one or more signal value data (for example, maximum point and minimum point) for each cycle, and based on the selected signal value data and the cycle of the adjusted waveform graph. A waveform graph consisting of cycles determined by each cycle may be newly generated by performing interpolation processing. For example, in a waveform graph that requires a cycle change, the maximum and minimum points of the signal value data are acquired, and based on the changed period and the acquired maximum and minimum point signal value data, bilinear interpolation and bicubic The signal value data may be interpolated by interpolation or the like to adjust the period of the waveform graph to generate the period adjustment data. According to this method, the cycle can be adjusted even when it cannot be dealt with by addition or thinning (signal value data cannot be added / deleted evenly).

Further, after adjusting the period, the amount of time shift of each period adjustment data for setting the phase of the start timing of the two period adjustment data to a predetermined phase (for example, the maximum point or the minimum point) is calculated. The signal value data of the cycle adjustment data is shifted in the time direction by the calculated shift amount. As a result, the phases of the start timings of the two period adjustment data can be matched.

Next, based on the past dynamic image from the signal value data of the signal value difference value of the same timing of the periodic adjustment data (for example, the periodic adjustment data (current periodic adjustment data) of the waveform graph generated based on the current dynamic image). The value obtained by subtracting the signal value data of the cycle adjustment data (past cycle adjustment data) of the generated waveform graph is calculated (step S23), and the difference graph is generated (step S24).
In step S24, for example, two periodic adjustment data (graphs) are combined into one, a waveform of the difference value is added on the graph, and the waveform of the difference value is colored according to the difference value to be a difference graph. To generate.

Then, the generated difference graph is displayed on the display unit 34 (step S25), and the difference display process B ends.

FIG. 7 is a diagram showing an example of the difference graph displayed in step S25. As shown in FIG. 7, in the difference graph, a waveform showing the time change of the feature amount in the past and present two dynamic images and a waveform showing the difference are superimposed and displayed. Further, at the timing when the current signal value is increasing as compared with the past, a color indicating that the signal value is increasing is displayed in the waveform showing the difference. At the timing when the current signal value is decreasing compared to the past, a color indicating that the signal value is decreasing is displayed on the waveform showing the difference in the difference graph. Therefore, the user can easily grasp the difference in the function of the diagnosis target between the dynamic images to be compared.

<Modified example of the second embodiment>
In the second embodiment, the case where two dynamic images obtained by photographing the dynamics of the subject are compared has been described. However, in the difference image display processing B, the dynamic images are pixel-by-pixel or a plurality of pixels. When comparing the analysis result images acquired by performing the dynamic analysis for each block (for example, the control unit 31 has a function of analyzing the dynamic image and generating the analysis result image, and analyzes the current dynamic image. It can also be applied (when comparing the analysis result image and the past analysis result image of the same patient stored in the storage unit 32). That is, by performing the same processing as in steps S21 to S25 of the difference display processing B for the two analysis result images to be compared, the difference can be visualized and easily grasped by the user.
Since the example of the analysis result image is the same as that described in the first embodiment, the description is incorporated.

<Third embodiment>
Next, a third embodiment of the present invention will be described.
The configuration in the third embodiment is the same as that described in the first embodiment, except that the program for executing the difference display process C is stored in the storage unit 32 of the diagnostic console 3. The description will be omitted, and the operation of the third embodiment will be described below.

First, dynamic imaging is performed by the imaging device 1 and the imaging console 2, a dynamic image is generated, and a series of frame images of the dynamic image is transmitted from the imaging console 2 to the diagnostic console 3.

In the diagnostic console 3, when a series of frame images of dynamic images whose function to be diagnosed is the function of the diaphragm is received from the photographing console 2 via the communication unit 35, they are stored in the control unit 31 and the storage unit 32. The difference display process C shown in FIG. 8 is executed in cooperation with the program.
FIG. 8 is a flowchart showing the difference display process C executed by the diagnostic console 3 in the third embodiment. The difference display process C is executed in collaboration with the program stored in the control unit 31 and the storage unit 32.

Hereinafter, the flow of the difference display process C will be described with reference to FIG.
First, a past dynamic image to be compared with the received dynamic image is selected (step S30).
Since the process of step S30 is the same as the process of step S10 of FIG. 3, the description is incorporated.

Next, the current dynamic image and the past dynamic image are subjected to warping processing to align the clavicle and the thorax (step S31).
For example, in step S31, first, the clavicle and the thorax are extracted from each of the frame image constituting the current dynamic image and the frame image constituting the past dynamic image. Extraction of the clavicle and sternum is performed by, for example, a method of performing template matching using a clavicle template, a rib template, and a sternum template prepared in advance in each frame image, or a method of applying a curve fitting function after edge detection. Can be done. In addition, based on the characteristics such as position, shape, size, concentration gradient, direction, etc. based on the prior knowledge of the structure of the clavicle and sternum, the extracted area is examined to see if it is the clavicle or sternum, and over-extracted. It may be possible to discriminate and remove the part. Next, one frame image is selected from all the frame images of the current dynamic image and the past dynamic image and used as the reference image so that the clavicle and sternum of the other frame images match the clavicle and sternum of the reference image. Is warped. The reference image may be a frame image of the first frame of the current dynamic image or the past dynamic image, or may be a frame image of the maximum expiratory position or the maximum inspiratory position.

Next, the feature amount (here, the diaphragm position) related to the function to be diagnosed is calculated from the current dynamic image and the past dynamic image, and the cycle of the time change of the calculated feature amount is acquired (step S32).
In step S32, first, the position of the diaphragm is specified from each frame image after each of the current dynamic image and the past dynamic image. In a plain radiograph of the front of the chest, the diaphragm appears to be in contact with the lower lung field. Therefore, for example, in each frame image, the lung field region can be extracted, and the contour of the lower part of the extracted lung field region can be specified as the position of the diaphragm.
Next, in each of the current dynamic image and the past dynamic image, the representative value (for example, mean value, median value, etc.) of the y-coordinate of the diaphragm position specified from each frame image is calculated, and the calculated representative value is used as the time. By plotting in a series (in the order of frame images), a waveform graph (called a waveform graph) showing the time change of the median position is generated. The horizontal direction of the image is the x direction, and the vertical direction is the y direction. Further, it is assumed that the origin is the upper left of the image and the coordinate value increases as the y direction goes down.
Then, from the generated waveform graph, the period of time change of the diaphragm position in each of the current dynamic image and the past dynamic image is acquired. The period can be calculated with the time from the maximum point (or minimum point) of the waveform indicating the time change of the diaphragm position to the next maximum point (or minimum point) as the period.

Next, the cycle is adjusted so that the cycle acquired from the current dynamic image and the cycle acquired from the past dynamic image match, and the cycle adjustment data is generated (step S33).
In step S33, as shown in FIG. 4, when the period acquired from the current dynamic image and the period acquired from the past dynamic image are different, the period is adjusted and two period adjustment data having the same period are generated. .. In the present embodiment, the cycle adjustment data is each of a plurality of dynamic images in which the cycles are matched (here, a current dynamic image and a past dynamic image in which the cycles are matched).

For example, first, the period of the adjusted dynamic image (the period of time change of the diaphragm position; the same applies hereinafter) is determined. As the adjusted cycle, a short cycle may be matched with a long cycle, or a long cycle may be matched with a short cycle. Further, both cycles may be adjusted to a predetermined cycle.
Next, in order to match the cycle of each dynamic image with the adjusted cycle, the number of frame images to be added or deleted for each cycle in each dynamic image is determined. If the number of frame images to be added or deleted is 0, the process of adjusting the period of the dynamic image is not performed. Then, by adding or deleting a determined number of frame images for each period of the dynamic image that needs to be adjusted and matching the periods of the two dynamic images, two dynamic images having the same period, that is, Two cycle adjustment data are generated.

For example, when matching a short cycle to a long cycle, frame images are evenly added to the dynamic image of the shorter cycle to match the cycle. The signal value of each pixel of the frame image to be added can be obtained, for example, by performing interpolation processing such as bilinear interpolation and bicubic interpolation using the signal values of a plurality of frame images of the original dynamic image. When adjusting the long cycle to the short cycle, the frame image is evenly thinned out (deleted) from the dynamic image of the longer cycle to match the cycle.

Alternatively, in a dynamic image that requires adjustment of the period, any one or more frame images (for example, an image corresponding to the maximum point and the minimum point of the diaphragm position) are selected for each period, and the selected frame image and the determined frame image are determined. By generating an interpolated image using bilinear interpolation, bicubic interpolation, or the like based on the number, a plurality of dynamic images having the same period of time change of the diaphragm position may be generated as the period adjustment data. According to this method, the cycle can be adjusted even when the frame image cannot be added / deleted evenly (the frame image cannot be added / deleted evenly).

Further, after adjusting the period, the phase of the start timing of the two period adjustment data is set to a predetermined phase (for example, the maximum point or the minimum point) of the time change of the diaphragm position in the time direction of each period adjustment data. The shift amount is calculated, and the signal value of the cycle adjustment data is shifted in the time direction by the calculated shift amount. As a result, the phases of the start timings of the two period adjustment data can be matched.

Next, the difference value of the diaphragm position between the frame images at the same timing of the two period adjustment data is calculated (step S34). Specifically, the difference value in the vertical direction between the diaphragm position of each frame image of the current cycle adjustment data and the diaphragm position of the frame image of the past cycle adjustment data at the same timing is calculated.

Next, based on the acquired difference information, a difference image in which the difference information is superimposed on each frame image of any of the periodic adjustment data is generated (step S35).
In step S35, for example, in each frame image of any of the periodic adjustment data (for example, the periodic adjustment data of the past dynamic image), different colors are applied to the current and past diaphragm positions and the region between them (difference region). A difference image is generated by superimposing. For example, a color corresponding to the sign of the difference value is superimposed on the difference region.

Then, the generated difference image is displayed on the display unit 34 (step S36), and the difference display process C ends.

FIG. 9 is a diagram showing a difference image displayed in step S36. As shown in FIG. 9, at the timing when the current diaphragm position is higher than the past (difference value is +), the current diaphragm position is in the past in the difference region between the current diaphragm position and the past diaphragm position. A color indicating higher is displayed. At the timing when the current diaphragm position is lower than the past (difference value is-), the color indicating that the current diaphragm position is lower than the past is displayed in the difference region between the current diaphragm position and the past diaphragm position. Is displayed. The larger the difference area indicating the absolute value of the difference value, the larger the change in function. Therefore, the user can easily grasp the difference between the dynamic images to be compared.

Although the first to third embodiments of the present invention have been described above, the description content in the embodiments is a preferable example of the present invention, and the description is not limited thereto.

For example, in the first embodiment and its modification, the phase of the start timing of the two periodic adjustment data is adjusted by shifting at least one of the plurality of periodic adjustment data relative to the time direction. However, the phase may be adjusted for each pixel of the periodic adjustment data corresponding to each other. For example, the blood flow in the lung field may be out of phase with the time change of the signal value near the heart and at the end, but the phase is uniformly uniform for all pixels as in the first embodiment and its modification. By shifting, the phase shift due to the pixel position is left as it is, so that the user can grasp the phase shift due to the position of each pixel in the dynamic image (analysis result image). On the other hand, by determining the amount of shift in the time direction for each pixel corresponding to each other in the periodic adjustment data and adjusting the phase so that the phases of all the pixels are aligned, the magnitude of the difference value of each phase depending on the pixel position is large. It makes it easier for users to judge the difference.

Further, when the type of the function to be diagnosed is the function of the diaphragm, a difference graph of the waveform graph of the diaphragm position of the two dynamic images to be compared may be generated and displayed on the display unit 34. The difference graph of the diaphragm position waveform graph is obtained by calculating the diaphragm position waveform graph by the method described in step S32 of FIG. 8 in step S21 of the difference display process B of FIG. 6, and step S22 to the generated waveform graph. It can be generated by performing the same processing as in step S24. In each step, the period is replaced with the period of the diaphragm position, and the signal value data is replaced with the diaphragm position data. Diaphragm position data refers to the value data of each diaphragm position plotted in the diaphragm position waveform graph.

Further, in the above embodiment, the case of generating the periodic adjustment data based on the two dynamic images to be compared or the two analysis result images has been described as an example, but the number of the dynamic images and the analysis result images to be compared is 2. The number is not limited to one, and may be two or more.

Further, in the above embodiment, the case where the output means is the display unit 34 has been described as an example, but for example, another output device such as a printer may be used.

Further, in the above embodiment, it has been described that the difference information (difference image or difference graph) from the dynamic image or the analysis result image is generated and displayed by a single device, but the processing may be divided by a plurality of devices. Good. For example, the generation and display of the difference information (difference image or difference graph) from the dynamic image or the analysis result image may be performed by separate devices.

Further, in the above embodiment, the case where the difference image is generated in the first and third embodiments and the difference graph is generated in the second embodiment has been described, but the diagnostic console 3 uses both the difference image and the difference graph. It may be provided with a function to generate. Then, the user may select which one to generate and display by the operation unit 33.

Further, for example, in the above description, an example in which a hard disk, a non-volatile memory of a semiconductor, or the like is used as a computer-readable medium of the program according to the present invention has been disclosed, but the present invention is not limited to this example. As another computer-readable medium, a portable recording medium such as a CD-ROM can be applied. A carrier wave is also applied as a medium for providing data of the program according to the present invention via a communication line.

In addition, the detailed configuration and detailed operation of each device constituting the dynamic analysis system can be appropriately changed without departing from the spirit of the present invention.

100 Dynamic analysis system 1 Imaging device 11 Radiation source 12 Radiation irradiation control device 13 Radiation detection unit 14 Reading control device 2 Imaging console 21 Control unit 22 Storage unit 23 Operation unit 24 Display unit 25 Communication unit 26 Bus 3 Diagnostic console 31 Control Unit 32 Storage unit 33 Operation unit 34 Display unit 35 Communication unit 36 Bus

Claims (20)

A graph showing the time change of the feature amount related to the function of the diagnosis target is generated from each of the plurality of dynamic images obtained by radiographing the dynamics of the living body, and the time change of the feature amount is based on the generated graph. Cycle acquisition means to acquire the cycle and
By adjusting at least one period of the graph showing the time change of the feature amount generated from the plurality of dynamic images, a plurality of periods of the feature amount with the same time change period are used as the plurality of period adjustment data. Period adjustment data generation means to generate graphs,
A difference information generating means for generating difference information for each of the same phases of the plurality of period adjustment data, and
An output means for outputting the difference information and
A dynamic analysis system equipped with. The cycle adjustment data generation means generates the plurality of cycle adjustment data in which the phases of the start timings match.
The dynamic analysis system according to claim 1, wherein the difference information generating means calculates a difference value of the feature amount at the same timing in the plurality of periodic adjustment data. The first dynamic image obtained by radiographing the dynamics of the living body is analyzed to generate the first analysis result image, and the second dynamic image obtained by radiographing the dynamics of the living body is obtained. An analysis means that analyzes and generates a second analysis result image,
A difference information generation means for generating difference information for each phase of the first analysis result image and the second analysis result image, and
An output means for outputting the difference information and
A dynamic analysis system equipped with. From the first analysis result image, the time change cycle of the first feature amount related to the function to be diagnosed, and from the second analysis result image, the time change of the second feature amount related to the function to be diagnosed. Cycle acquisition means to acquire the cycle and
The first analysis result image and the first analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other by adjusting the cycle acquired by the cycle acquisition means. Period adjustment data generation means for generating the second analysis result image,
The dynamic analysis system according to claim 3. The period adjustment data generation means adds or deletes a frame image to at least one of the first analysis result image and the second analysis result image, so that the period of time change of the first feature amount can be obtained. The dynamic analysis system according to claim 4, wherein the first analysis result image and the second analysis result image have the same period of time change of the second feature amount. The period adjustment data generation means adds a signal value of each pixel in a frame image to be added to at least one of the first analysis result image and the second analysis result image to a plurality of frames of the added analysis result image. The dynamic analysis system according to claim 5, wherein the dynamic analysis system is calculated by interpolating using the signal values of pixels at the same position in the image. The period adjustment data generation means generates an interpolated image based on signal values of a plurality of frame images selected from at least one of the first analysis result image and the second analysis result image. The fourth aspect of claim 4, wherein the first analysis result image and the second analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other. Dynamic analysis system. The period adjustment data generation means generates the first analysis result image and the second analysis result image in which the phases of the start timings match.
The difference information generating means calculates the difference value of the signal value between the pixels of the same coordinates of the frame image of the same timing in the first analysis result image and the second analysis result image. The dynamic analysis system according to any one of the items. The cycle acquisition means has a graph showing a time change of the feature amount related to the function of the diagnosis target from the first analysis result image, and a time of the feature amount related to the function of the diagnosis target from the second analysis result image. A graph showing the change is generated, and the time change cycle of the first feature amount and the time change cycle of the second feature amount are acquired based on the generated graph.
The period adjustment data generating means includes a graph showing a time change of the first feature amount generated from the first analysis result image and a time of the second feature amount generated from the second analysis result image. Claim to generate a plurality of graphs in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other by adjusting at least one cycle of the graph showing the change. 4. The dynamic analysis system according to 4. The period adjustment data generation means generates the first analysis result image and the second analysis result image in which the phases of the start timings match.
The dynamic analysis system according to claim 9, wherein the difference information generating means calculates a difference value of signal values at the same timing between the first analysis result image and the second analysis result image. The dynamic analysis system according to any one of claims 3 to 10, wherein the first dynamic image and the second dynamic image are dynamic images of the chest. The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the blood flow function or the ventilation function of the lung field.
The dynamic analysis system according to any one of claims 4 to 10, wherein the first feature amount and the second feature amount are signal values of pixels in a region of interest. The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the function of the diaphragm.
The dynamic analysis system according to any one of claims 4 to 10, wherein the first feature amount and the second feature amount are diaphragm positions. The dynamic analysis system according to any one of claims 3 to 13, wherein the output means synthesizes and outputs the difference information with at least one of the first analysis result image and the second analysis result image. .. Computer,
The first dynamic image obtained by radiographing the dynamics of the living body is analyzed to generate the first analysis result image, and the second dynamic image obtained by radiographing the dynamics of the living body is obtained. An analysis means that analyzes and generates a second analysis result image,
A difference information generation means for generating difference information for each phase of the first analysis result image and the second analysis result image.
An output means for outputting the difference information,
A program to function as. The computer,
From the first analysis result image, the time change cycle of the first feature amount related to the function to be diagnosed, and from the second analysis result image, the time change of the second feature amount related to the function to be diagnosed. Cycle acquisition means to acquire the cycle and
The first analysis result image and the first analysis result image in which the time change cycle of the first feature amount and the time change cycle of the second feature amount are equal to each other by adjusting the cycle acquired by the cycle acquisition means. Periodic adjustment data generation means for generating the second analysis result image,
The program according to claim 15, which functions as. The program according to claim 15 or 16, wherein the first dynamic image and the second dynamic image are dynamic images of the chest. The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the blood flow function or the ventilation function of the lung field.
The program according to claim 16, wherein the first feature amount and the second feature amount are signal values of pixels in a region of interest. The first dynamic image and the second dynamic image are dynamic images of the chest.
The function to be diagnosed is the function of the diaphragm.
The program according to claim 16, wherein the first feature amount and the second feature amount are diaphragm positions. The program according to any one of claims 15 to 19, wherein the output means synthesizes and outputs the difference information with at least one of the first analysis result image and the second analysis result image.