JP6436182B2 - Dynamic image analyzer - Google Patents

Description

  The present invention relates to a dynamic image analysis apparatus.

In contrast to the conventional still image and diagnosis of radiation using a film / screen or photostimulable phosphor plate, a dynamic image of the region to be examined is taken using a semiconductor image sensor such as an FPD (flat panel detector), Attempts have been made to apply it to diagnosis. Specifically, by utilizing the responsiveness of reading / erasing of image data of the semiconductor image sensor, pulsed radiation is continuously irradiated from the radiation source in accordance with the reading / erasing timing of the semiconductor image sensor. Take multiple shots per second to capture the dynamics of the area to be examined. By sequentially displaying a series of a plurality of images acquired by imaging, a doctor can recognize a series of movements of a region to be examined.

  Various techniques for displaying dynamic images in an easy-to-view manner have also been proposed. For example, Patent Document 1 describes a technique for creating a difference image between frames of a dynamic image and displaying the difference moving image.

JP 2004-31434 A

  An object of the present invention is to provide diagnosis support information about a ventilation state based on an image obtained by dynamic imaging of a chest.

In order to solve the above-mentioned problem, a dynamic image analyzer of the invention according to claim 1
A reference image is defined from a plurality of frame images showing the dynamics of the chest obtained by dynamic imaging of the human chest, and the reference image is divided into a plurality of small regions. Area dividing means for calculating small areas corresponding to a plurality of small areas of the reference image in frame images other than the reference image,
An analysis unit that performs image analysis for each corresponding small area in the plurality of frame images, and obtains ventilation state information for each small area;
With
It said analyzing means, before Symbol small regions each, area change relative to the reference image and acquires a timing which exceeds a predetermined value as the information of the ventilation.

The invention according to claim 2 is the invention according to claim 1,
The analysis unit determines that an area in which the timing acquired for each small area exceeds a predetermined value is abnormal .

  ADVANTAGE OF THE INVENTION According to this invention, it becomes possible to provide the diagnostic assistance information about the state of ventilation based on the image obtained by carrying out dynamic imaging | photography of the chest.

It is a figure which shows the example of whole structure of the dynamic image diagnosis assistance system in embodiment of this invention. It is a flowchart which shows the imaging | photography control processing performed by the control part of the imaging | photography console shown in FIG. It is a flowchart which shows the image analysis process performed by the control part of the arithmetic unit shown in FIG. It is a flowchart which shows the area | region division process performed by the control part of the arithmetic unit shown in FIG. It is a figure for demonstrating the small area | region acquired by the area | region division process of FIG. It is a flowchart which shows the arousal determination process performed by the control part of the arithmetic unit shown in FIG. (A) is a figure for demonstrating the periphery area | region used for determination of abnormality in the arousal determination process of FIG. 6, (b) is a periphery used for determination of abnormality in the arousal determination process of FIG. 6 when a small area | region is small. It is a figure for demonstrating an area | region. (A) is a figure for demonstrating the left and right lung field area | region used for determination of abnormality in the arousal determination process of FIG. 6, (b) determines abnormality in the arousal determination process of FIG. 6 when a small area | region is small. It is a figure for demonstrating the left and right lung field area | region used for. It is a flowchart which shows the blood-flow determination process performed by the control part of the arithmetic unit shown in FIG. It is a flowchart which shows the display control process performed by the control part of the diagnostic console shown in FIG. It is a figure which shows an example of the determination result display screen displayed on the display part of the diagnostic console shown in FIG.

Hereinafter, an embodiment according to the present invention will be described. However, the present invention is not limited to the illustrated example.
[Configuration of Dynamic Image Diagnosis Support System 100]
First, the configuration will be described.

  FIG. 1 shows the overall configuration of a dynamic image diagnosis support system 100 in the present embodiment.

As shown in FIG. 1, in the dynamic image diagnosis support system 100, an imaging device 1 and an imaging console 2 are connected by a communication cable or the like, an imaging console 2, a diagnostic console 3, an arithmetic device 4, The image server 5 is connected via a communication network NT such as a LAN (Local Area Network). Each device constituting the dynamic image diagnosis support system 100 conforms to the DICOM (Digital Image and Communications in Medicine) standard, and communication between the devices is performed according to DICOM.
[Configuration of the photographing apparatus 1]
The imaging apparatus 1 is an apparatus that performs dynamic imaging of the chest of a human body including, for example, pulmonary expansion and contraction morphological changes associated with breathing, heart pulsation, and the like. Dynamic imaging is performed by continuously irradiating a human chest with radiation such as X-rays to acquire a plurality of images (that is, continuous imaging). A series of images obtained by this continuous shooting is called a dynamic image. Each of the plurality of images constituting the dynamic image is called a frame image.

  As shown in FIG. 1, the imaging apparatus 1 includes a radiation source 11, a radiation irradiation control device 12, a radiation detection unit 13, a reading control device 14, a cycle detection sensor 15, a cycle detection device 16, and the like.

  The radiation source 11 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 radiation irradiation conditions input from the imaging console 2 to perform radiation imaging. The radiation irradiation conditions input from the imaging console 2 are, for example, pulse rate, pulse width, pulse interval, imaging start / end timing, X-ray tube current value, X-ray tube voltage value, filter type during continuous irradiation. Etc. The pulse rate is the number of times of radiation irradiation per second, and matches the frame rate described later. The pulse width is a radiation irradiation time per one irradiation. The pulse interval is the time from the start of one radiation irradiation to the start of the next radiation irradiation in continuous imaging, and coincides with a frame interval described later.

  The radiation detection unit 13 is configured by a semiconductor image sensor such as an FPD. The FPD has, for example, a glass substrate or the like, detects radiation that has been irradiated from the radiation source 11 and transmitted through at least the subject M at a predetermined position on the substrate according to its intensity, and detects the detected radiation as an electrical signal. A plurality of pixels to be converted and stored are arranged in a matrix. Each pixel includes a switching unit such as a TFT (Thin Film Transistor).

  The reading control device 14 is connected to the imaging 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 imaging console 2 to switch the reading of the electrical signal accumulated in each pixel. Then, the image data is acquired by reading the electrical signal accumulated in the radiation detection unit 13. Then, the reading control device 14 outputs the acquired image data to the imaging 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 and matches 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 in continuous shooting, and coincides 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 to synchronize the radiation irradiation operation and the image reading operation.

  The cycle detection sensor 15 detects the respiratory motion state of the subject M and outputs detection information to the cycle detection device 16. As the cycle detection sensor 15, for example, a respiration monitor belt, a CCD (Charge Coupled Device) camera, an optical camera, a spirometer, or the like can be applied.

Based on the detection information input by the cycle detection sensor 15, the cycle detection device 16 determines the number of respiratory cycles and the state during one cycle of the current respiratory motion (for example, inspiration, inspiration to expiration conversion point, The state of the conversion point of exhalation and exhalation to inspiration is detected, and the detection result (cycle information) is output to the control unit 21 of the imaging console 2. The cycle detection device 16 receives, for example, detection information indicating that the state of the lung is a conversion point from inspiration to expiration by a cycle detection sensor 15 (respiration monitor belt, CCD camera, optical camera, spirometer, etc.). The timing is set as the base point of one cycle, and the period until the next timing when this state is detected is recognized as one cycle.
[Configuration of the shooting console 2]
The imaging console 2 outputs radiation irradiation conditions and image reading conditions to the imaging apparatus 1 to control radiation imaging and radiation image reading operations by the imaging apparatus 1, and also captures image data acquired by the imaging apparatus 1. Displayed for confirmation of whether the image is suitable for confirmation of positioning or diagnosis.

  As shown in FIG. 1, the imaging 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 includes a CPU (Central Processing Unit) and a RAM (Random Access Memory).
) Etc. The CPU of the control unit 21 reads out the system program and various processing programs stored in the storage unit 22 in accordance with the operation of the operation unit 23 and expands them in the RAM. The operation and the radiation irradiation operation and reading operation of the imaging apparatus 1 are centrally controlled.

  The storage unit 22 is configured by a nonvolatile semiconductor memory, a hard disk, or the like. The storage unit 22 stores various programs executed by the control unit 21 and data such as parameters necessary for execution of processing by the programs or processing results. For example, the storage unit 22 stores a shooting control processing program for controlling the shooting flow shown in FIG. In addition, the storage unit 22 stores radiation irradiation conditions and image reading conditions in association with the examination target region. 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 includes a keyboard having a cursor key, numeric input keys, various function keys, and the like, and a pointing device such as a mouse. The control unit 23 controls an instruction signal input by key operation or mouse operation on the keyboard. To 21. In addition, the operation unit 23 may include a touch panel on the display screen of the display unit 24. 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 configured by a monitor such as an LCD (Liquid Crystal Display) or a CRT (Cathode Ray Tube), and displays an input instruction, data, or the like from the operation unit 23 in accordance with an instruction of a display signal 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 terminal that acquires image data of a dynamic image from the image server 5, displays a dynamic image based on the acquired image data, and makes a diagnostic interpretation by 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 includes a CPU, a 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 in accordance with the operation of the operation unit 33 and expands them in the RAM, and displays control described later according to the expanded programs. Various processes including the process are executed to centrally control the operation of each part of the diagnostic console 3.

  The storage unit 32 is configured by a nonvolatile semiconductor memory, a hard disk, or the like. The storage unit 32 stores various programs and programs including the display control processing program executed by the control unit 31 and parameters such as parameters necessary for execution of processing or data such as processing results. These various programs are stored in the form of readable program codes, and the control unit 31 sequentially executes operations according to the program codes.

  The operation unit 33 includes a keyboard having cursor keys, numeric input keys, various function keys, and the like, and a pointing device such as a mouse. The control unit 33 controls an instruction signal input by key operation or mouse operation on the keyboard. To 31. The operation unit 33 may include a touch panel on the display screen of the display unit 34, and in this case, an instruction signal input via the touch panel is output to the control unit 31.

  The display unit 34 as a display unit is configured by a monitor such as an LCD or a CRT, and displays an input instruction, data, or the like from the operation unit 33 in accordance with an instruction of a display signal input from the control unit 31.

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.
[Configuration of the arithmetic unit 4]
The arithmetic device 4 performs image analysis processing on the image data of the dynamic image transmitted from the imaging console 2 and transmits it to the image server 5.

  As shown in FIG. 1, the arithmetic device 4 includes a control unit 41, a storage unit 42, a communication unit 43, and the like, and each unit is connected by a bus 44.

  The control unit 41 includes a CPU, a RAM, and the like. The CPU of the control unit 41 reads out the system program and various processing programs stored in the storage unit 42 and expands them in the RAM, and executes various processes including image analysis processing described later according to the expanded programs. Then, the operation of each part of the arithmetic unit 4 is centrally controlled.

  The storage unit 42 is configured by a nonvolatile semiconductor memory, a hard disk, or the like. The storage unit 42 stores various programs and programs including the image analysis processing program executed by the control unit 41 and parameters such as parameters necessary for execution of processing or data such as processing results. These various programs are stored in the form of readable program codes, and the control unit 41 sequentially executes operations according to the program codes.

The communication unit 43 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.
[Configuration of Image Server 5]
The image server 5 is a computer device that has a storage device composed of a hard disk or the like, and stores and manages the image data of the dynamic image transmitted from the arithmetic device 4 in the storage device so as to be searchable. When a dynamic image acquisition request is transmitted from the diagnostic console 3, the image server 5 reads out the requested dynamic image data from the storage device and transmits it to the diagnostic console 3.
[Operation of Dynamic Image Diagnosis Support System 100]
Next, the operation in the dynamic image diagnosis support system 100 will be described.
(Shooting operation)
First, the flow of imaging in the dynamic image diagnosis support system 100 will be described.

  FIG. 2 shows a photographing flow executed in the photographing apparatus 1 and the photographing console 2.

  First, the operation unit 23 of the imaging console 2 is operated by the imaging engineer, and patient information (patient name, height, weight, age, sex, etc.) of the imaging target (subject M) is input (step S1).

  Next, the radiation irradiation conditions are read from the storage unit 22 and set in the radiation irradiation control device 12 by the control unit 21 of the imaging console 2, and the image reading conditions are read from the storage unit 22 and read control device. 14 is set (step S2).

  Next, the radiation irradiation instruction by the operation of the operation unit 23 is waited. When the radiation irradiation instruction is input by the operation unit 23 (step S3; YES), the control unit 21 instructs the cycle detection device 16 to start cycle detection. Is output, and the cycle detection of the breathing motion of the subject M by the cycle detection sensor 15 and the cycle detection device 16 is started (step S4). When the cycle detection device 16 detects a predetermined state (here, a conversion point from inspiration to expiration), the control unit 21 outputs an imaging start instruction to the radiation irradiation control device 12 and the reading control device 14. Then, dynamic imaging is started (step S5). That is, radiation is emitted from the radiation source 11 at a pulse interval set in the radiation irradiation control device 12, and image data (frame image) is acquired by the radiation detection unit 13. When the cycle detecting device 16 detects a predetermined number of dynamic cycles, the control unit 21 outputs an instruction to end imaging to the radiation irradiation control device 12 and the reading control device 14, and the imaging operation is stopped.

  Image data acquired by shooting is sequentially input to the shooting console 2, and is stored in the storage unit 22 in association with a number indicating the shooting order by the control unit 21 (step S6) and displayed on the display unit 24. (Step S7). The imaging engineer confirms the positioning and the like based on the displayed dynamic image, and determines whether an image suitable for diagnosis is acquired by imaging (imaging OK) or re-imaging is necessary (imaging NG). Then, the operation unit 23 is operated to input a determination result.

When a judgment result indicating photographing OK is input by a predetermined operation of the operation unit 23 (step S8; YES), a series of image data acquired by dynamic photographing, that is, a series of frame images is respectively input by the control unit 21. Identification information for identifying a dynamic image, information such as patient information, examination site, radiation irradiation conditions, image reading conditions, imaging order number, cycle information, etc. are attached (for example, image data in DICOM format) Is written in the header area) and transmitted to the arithmetic unit 4 via the communication unit 25 (step S9). Then, this process ends. On the other hand, when a determination result indicating photographing NG is input by a predetermined operation of the operation unit 23 (step S8; NO), a series of image data stored in the storage unit 22 is deleted by the control unit 21 (step S10). ), This process ends.
(Operation of the arithmetic unit 4)
Next, the operation in the arithmetic device 4 will be described.

  In the arithmetic unit 4, when a series of dynamic image data is received from the imaging console 2 via the communication unit 43, the control unit 41 and the image analysis processing program stored in the storage unit 42 cooperate. Thus, the image analysis process shown in FIG. 3 is executed.

  In the image analysis process, first, an area division process is executed (step S11).

  FIG. 4 shows a flow of the area division process. This process is realized by the cooperation of the control unit 41 and the area division processing program stored in the storage unit 42.

  First, a reference image (referred to as a reference image P1) is set from a plurality of frame images constituting a dynamic image (step S101). The reference image P1 may be any frame image, but here, the reference image P1 will be described as the first (first) frame image. That is, the reference image P1 in the present embodiment will be described as an image that is captured at the inspiration → expiration conversion point and has the maximum lung field area in one respiratory cycle.

  Next, the lung field region is extracted from the reference image P1 (step S102).

  Since the lung field region has a large amount of transmission of radiation (X-rays), the signal value is higher than the surrounding region. Therefore, for example, a lung field region is extracted by the following process.

  First, a density histogram is created from the signal value of each pixel, and a threshold value is obtained by a discriminant analysis method or the like. Next, a region having a signal higher than the obtained threshold is extracted as a lung field region candidate. Next, edge detection is performed near the boundary of the candidate area, and a point where the edge is maximum in a small area near the boundary is extracted along the boundary. Then, the extracted edge point is approximated by a polynomial function to obtain a boundary line of the lung field region.

  Next, a rectangular area including the extracted lung field area is set, and the rectangular area is divided into 0.4 to 4 cm square small areas A1 (indicated by dotted lines in FIG. 5) (step S103).

  Next, 1 is set to the counter n (step S104), and local matching processing is performed to determine which position in the (n + 1) th frame image each small region A1 in the nth frame image of the shooting order corresponds to. (Step S105).

  The local matching process can be performed, for example, by a method described in Japanese Patent Application Laid-Open No. 2001-157667. Specifically, first, the search area of each small area A1 in the frame image with the shooting order n is set in the frame image with the shooting order (n + 1). Here, each search region set in the (n + 1) th frame image has the same center point (x, y) when the coordinates of the center point in each small region A1 in the nth frame image are (x, y). x, y), and the vertical and horizontal widths are set to be larger than each small area A1 of the nth frame image (for example, the vertical and horizontal widths are each doubled).

  Next, for each small area A1 of the nth frame image, a position having the highest matching degree in the search area set in the (n + 1) th frame image is calculated, and the position on the (n + 1) th frame image is calculated. Calculated as the corresponding position. As the degree of matching, a least square method or a cross-correlation coefficient is used as an index.

  When it is calculated by the local matching processing which position (small area) of the (n + 1) th frame image corresponds to each small area A1 of the nth frame image in the shooting order, in the (n + 1) th frame image The coordinates (x ′, y ′) of the center point of each small area A1 are acquired as positions corresponding to the coordinates (x, y) of the center point of each small area A1 of the nth frame image and stored in the RAM. (Step S106).

  Next, it is determined whether or not (n + 1)> the number of frame images. If it is determined that (n + 1)> the number of frame images is not satisfied (step S107; NO), the counter n is incremented by 1 (step S108). The process returns to step S105. If it is determined that (n + 1)> the number of frame images (step S107; YES), each frame image has a new small area whose apex is the center point of each small area A1, as indicated by a solid line in FIG. The area is divided into A2 (step S109), the area dividing process is completed, and the process proceeds to step S12 in FIG.

  In the region dividing process described above, the small region A1 is generated by dividing the region including the lung field region in the reference image P1 into vertical and horizontal equal intervals (0.4 to 4 cm). However, the blood vessel region in the lung field in the frame image is generated. It is also possible to obtain a structurally characteristic point such as a blood vessel bifurcation point by extracting (details will be described later), and use a rectangular area centered on the obtained point as a small area A1 as a target area for local matching processing. .

  Further, in the above-described region dividing process, the local matching process is performed on the image data of each frame image itself. However, the local matching process may be performed on an image whose edge is extracted by a gradient filter or the like. At this time, in order to eliminate the influence of the ribs, it is preferable to recognize the ribs from each frame image and exclude only the edges of the ribs. For example, as proposed in Japanese Patent Laid-Open No. 2005-20338, the recognition of the rib portion in each frame image is performed by using the initial shape of the rib detected by edge detection (parabolic approximate shape detection) as the rib shape model (teacher data). To generate an arbitrary rib shape as a linear sum of the average shape obtained from the above and a plurality of principal component shapes obtained by principal component analysis of teacher data) to obtain a model projection shape of the rib Can be applied.

  In step S12 of FIG. 3, an arousal determination process is executed.

  FIG. 6 shows a flow of the arousal determination process. This process is realized by cooperation between the control unit 41 and the arousal determination processing program stored in the storage unit 42.

  First, in each frame image, for each newly generated small region A2, the area change rate with respect to the reference image P1 (specifically, the area change rate with respect to the corresponding small region A2 in the reference image P1), and An area change rate with respect to the previous frame image in the shooting order (specifically, an area change rate with respect to the corresponding small region A2 in the previous frame image in the shooting order) is calculated (step S201). . Here, the area change rate with respect to the reference image P1 for each small region A2 of each frame image is, for example, the small region corresponding to the reference image P1 in the area (a) of each small region A2 of each frame image. It can be determined by the value (a / b) of the ratio of A2 to the area (b). Similarly, the area change rate for each small region A2 of each frame image with respect to the frame image in the previous shooting order is, for example, the area of each small region A2 of each frame image (referred to as a) in the shooting order. Can be obtained by the ratio value (a / c) to the area (referred to as c) of the corresponding small region A2. The area of each small region A2 can be obtained based on the number of pixels counted in the small region A2.

Next, an analysis is performed using the area change rate with respect to the reference image P1 and the area change rate with respect to the previous frame image calculated for each small region A2 in each frame image, and for each small region A2, It is determined whether or not the state of arousal is abnormal (step S202). In step S202, it is determined whether or not the state of arousal is abnormal mainly by checking the consistency with the behavior of the surrounding small area and the consistency of the area change rate with respect to the temporal change. For example, for each small region A2 in each frame image, the area change rate with respect to the reference image P1 and the area change rate with respect to the previous frame image are compared in the peripheral, left and right lung fields, and upper and lower lung fields, respectively. To do.
[Nearby]
The vertical positions (positions in the vertical direction) are substantially the same for the area change rates of the small regions A2 in each frame image (the area change rate with respect to the reference image P1 and the area change rate with respect to the previous frame image). A comparison is made with the average value of the area change rate in a plurality of small regions A2 around the lung field (left lung field or right lung field). Then, the small area A2 that exceeds a predetermined range (for example, the average value ± 20%) with respect to the obtained average value is determined to be abnormal. For example, for the small region A2 indicated by a bold line in FIG. 7A, the average value is determined in advance by comparing with the average value of the area change rates in the plurality of small regions A2 in the region surrounded by the dotted line in FIG. It is determined whether or not there is an abnormality depending on whether or not the specified range is exceeded. When the size of each small area A2 is smaller than a predetermined size, as shown in FIG. 7B, the area for obtaining the average value of the area change rate may be a plurality of rows.

For each small region A2 determined to be abnormal, it is determined whether the area change (area increase / decrease amount) is too large or too small compared to the surrounding area. For example, when the reference image P1 is an image having the largest lung field area as in the present embodiment, this determination can be made according to the following criteria 1) and 2).
1) When it is determined as abnormal based on the area change rate with respect to the reference image P1. The area change rate is smaller than the average value of the surrounding area change rate minus 20% → the area change is large (change from the reference image P1 (reduction rate) ) Is big)
The area change rate is larger than the average value of the surrounding area change rate + 20% → the area change is small (the change (reduction rate) from the reference image P1 is small)
2) When it is determined as abnormal based on the area change rate with respect to the previous frame image a) During exhalation ・ The area change rate is smaller than the average value of the surrounding area change rate minus 20% → the area change is large (one The change (reduction ratio) from the previous frame image is large)
-The area change rate is larger than the average value of the surrounding area change rate + 20% → The area change is small (change (reduction rate) from the previous frame image is small)
b) During inspiration ・ Area change rate is smaller than the average value of the surrounding area change rate minus 20% → Area change is small (change (expansion rate) from the previous frame image is small)
-The area change rate is larger than the average value of the surrounding area change rate + 20% → The area change is large (the change (expansion rate) from the previous frame image is large)
In the header area of the frame image having the small area A2 determined to be abnormal, information indicating the type of abnormality (for example, a code indicating “arousal: surrounding”), the small area A2 determined to be abnormal Position information (for example, coordinates of four vertices of the small area A2), information for identifying the type of area change rate determined to be abnormal (for example, the area change rate with respect to the reference image P1 or the previous frame image) Code for identifying which of the area change rates is abnormal, etc.), the reason for determining the abnormality (code indicating whether the area change (area increase / decrease amount) is too large or too small compared to the surroundings, etc.) ) Is written in association with each other.

By performing the above-described determination, the small area A2 that behaves differently from the surrounding area can be detected as an abnormal part.
[Left and right lung fields]
In the left and right lung field regions of each frame image, the area change rate of the small region A2 whose vertical position (position in the vertical direction) is substantially the same (area change rate with respect to the reference image P1, area change rate with respect to the previous frame image) Are averaged to calculate an average value, and the average values of the left and right lung field regions having substantially the same vertical position are compared. When one average value exceeds a predetermined range with respect to the other average value (for example, the average value of the paired lung fields ± 20%), the left and right lung field regions are included. All small areas A2 are determined to be abnormal. For example, the average value of the area change rate of the small region A2 included in the region B1 surrounded by the oblique line illustrated in FIG. 8A is compared with the average value of the area change rate of the small region A2 included in the region B2, As a result, when it exceeds the predetermined range, all the small areas A2 included in the areas B1 and B2 are determined to be abnormal. When the size of the small area A2 is smaller than the predetermined size, as shown in FIG. 8B, the area for obtaining the average value of the area change rate may be a plurality of rows.

Are the left and right lung field areas determined to be abnormal larger than the paired lung field areas (areas where the vertical positions of the other left and right lung fields are approximately the same)? Or determine if it is too small. For example, when the reference image P1 is an image having the largest lung field area as in the present embodiment, this determination can be made according to the following criteria 1) and 2).
1) When it is determined as abnormal based on the area change rate with respect to the reference image P1-The average value of the area change rate is smaller than the average value of the area change rate of the pulmonary field region minus 20%-> The area change is large (reference) (Change from image P1 (reduction rate) is large)
-The average value of the area change rate is larger than the average value of the area change rate of the lung field region + 20%, and the area change is small (the change (reduction rate) from the reference image P1 is small).
2) When it is determined as abnormal based on the area change rate with respect to the previous frame image a) During exhalation ・ The average value of the area change rate is smaller than the average value of the area change rate of the corresponding lung field region minus 20% → Area change is large (change from the previous frame image (reduction ratio) is large)
-The average value of the area change rate is greater than the average value of the area change rate of the lung field region + 20% → the area change is small (the change (reduction rate) from the previous frame image is small)
b) At the time of inhalation ・ The average value of the area change rate of the lung field region where the average value of the area change rate is smaller than −20% → the area change is small (the change (expansion rate) from the previous frame image is small) small)
-The average value of the area change rate is larger than the average value of the area change rate of the lung field region + 20% → the area change is large (the change (expansion rate) from the previous frame image is large)
In the header area of the frame image where there is a small area A2 determined to be abnormal, information indicating the type of abnormality (for example, a code indicating “arousal: left and right lung fields”), and the small area A2 determined to be abnormal Position information (for example, coordinates of the four vertices of the small area A2), information for identifying the area change rate determined to be abnormal (for example, the area change rate with the reference image P1 or the previous frame image) For identifying which of the area change rates is abnormal, and the reason why each small area A is determined to be abnormal (a pair of lung field areas (areas where the vertical positions of the other left and right lung fields are substantially the same) )) And the like indicating whether the area change is too large or too small compared to)) is written in association with each other.

By performing the above-described determination, it is possible to detect a region in which the right and left behaviors are unbalanced as abnormal.
[Upper and lower lung fields]
First, the area change rate maximum value (maximum area / minimum area) between frame images for one cycle of respiratory motion is calculated for each small area A2, and the calculated small areas in the left and right lung field areas are calculated. The area change rate maximum value of A2 is averaged in the horizontal direction (in the row direction), and the average value of the area change rate maximum values of a plurality of small regions A2 having substantially the same vertical position is calculated. Then, a portion contrary to the normal operation that “the area change rate is smaller in the upper lung field” is determined to be abnormal (first example). Specifically, when there is a place at a vertical position located below each vertical position that is smaller than the average value of the area change rate maximum values calculated at the vertical position, all the small areas A2 belonging to the vertical position are abnormally detected. Is determined. As another example, the average value of the maximum area change rate at each vertical position is compared with the normal value (standard value) of the maximum area change rate according to the vertical position from the lung bottom. If it exceeds a predetermined range (for example, normal value ± 20%), all the small areas A2 in the vertical position are determined to be abnormal. The normal value described above is a function of the vertical position from the lung bottom. The function of the normal value is determined in advance according to patient information (age, height, sex) and imaging state (normal / deep breathing).

  In addition, a portion that is contrary to normal operation that “the area change is the upper lung field and the change start timing is delayed (the change timing is delayed with respect to the lung bottom)” is determined to be abnormal (second example). Specifically, when there is a place where the area change start timing is later than the vertical position at a vertical position located below each vertical position, all the small areas A2 belonging to the vertical position are determined to be abnormal. The area change start timing is a timing at which the area change rate with respect to the reference image P1 exceeds a predetermined value. This timing can be counted by the number of images from the reference image P1 to a frame image whose area change rate with respect to the reference image P1 exceeds a predetermined value. As another example, an area change start timing at each vertical position is compared with a normal value (standard value) of the area change start timing according to the vertical position from the lung bottom, and a predetermined range for the normal value When it exceeds (for example, normal value ± 20%), all the small areas A2 in the vertical position are determined to be abnormal. The normal value described above is a function of the vertical position from the lung bottom. The function of the normal value is determined according to patient information (age, height, sex) and imaging state (during normal / deep breathing). In comparison with the normal value, the measurement data (the timing at which the area change rate from the reference image P1 becomes equal to or greater than the predetermined value) is normalized so that the normal value and the respiratory cycle coincide (the area from the reference image P1). Comparison may be made after calculating the timing at which the rate of change is equal to or greater than a predetermined value / the respiratory cycle at the time of frame image shooting × the respiratory cycle of the normal value.

  When there is a small area determined to be abnormal in the first example, information indicating the type of abnormality (for example, “arousal: upper and lower lung fields (maximum area change rate)” is displayed in the header area or the like of the reference image P1. The position information of the small area A2 determined to be abnormal (for example, the coordinates of the four vertices of the small area A2). If there is a small area A2 determined to be abnormal in the second example, the type of abnormality (for example, a code indicating “arousal: upper and lower lung fields (area change start timing)”) in the header area or the like of the reference image P1 The position information of the small area A2 determined to be abnormal (for example, the coordinates of the four vertices of the small area A2) is written.

  By performing the above-described determination, normality in standing imaging can be verified and an abnormality can be detected. In the first example described above, an abnormality is detected by comparing the upper and lower sides within the data of one patient and in the second example by comparing the absolute value with a normal value (standard value).

  When the determination in step S202 ends, the process proceeds to step S13 in FIG. 3, and a blood flow determination process is executed.

  FIG. 9 shows a flow of blood flow determination processing. This process is realized by cooperation between the control unit 41 and the blood flow determination processing program stored in the storage unit 42.

  First, in each frame image, a heart region is extracted, a cardiac cycle is recognized from a shape change of the cardiac region, and each frame image is associated with a cardiac cycle (step S301).

  Extraction of the heart region in each frame image is performed by the following processing, for example.

  First, the lung field region is recognized. Next, the search area is limited from the circumscribed rectangular area of the lung field area. Next, a density histogram is created from the signal value of each pixel in the search region, a threshold value is obtained by a discriminant analysis method or the like, and a region having a signal lower than the threshold value is extracted as a candidate region for the heart. Next, edge detection is performed within the candidate region, and the contour line of the heart region is extracted by tracking the maximum value of the differential value greater than or equal to a predetermined size. At this time, the contour edge point search region is limited based on the shape of the approximate heart region so as not to track the background or the edge inside the heart. Then, template matching is performed on the extracted contour image of the heart region using a heart contour template, and the template region at the position where the correlation value is maximized is recognized as the heart region. Here, the cardiac contour template is a template of the timing when the ventricle changes from diastole to systole in the cardiac cycle, a template of the ventricular systole, a template of the timing when the ventricle changes from systole to diastole, Prepare a template for each state that the ventricle can take in the cardiac cycle, such as a template, and recognize the frame image that maximizes the correlation value with the template for each ventricular state in the cardiac cycle as a frame image that shows that state To do. An electrocardiograph is attached to the patient at the time of radiographing, and data on the electrocardiographic waveform is collected at the same time as radiation irradiation. Based on the obtained electrocardiographic waveform, each frame image is displayed in the cardiac cycle in the radiographing console 2. It may be determined whether the image corresponds to the state and written in advance in the header area of each frame image.

  In step S301, after extracting the heart region in each frame image, a series of images from the predetermined timing in the cardiac cycle to the next same timing (here, for example, from the timing when the ventricle changes from the diastole to the systole, (A series of frame images from the time when the ventricle changes from the diastole to the systole) is extracted as one cardiac cycle unit. A number identifying a cardiac cycle unit (here, a continuous number starting from 1) is written in the header area of each frame image, and at least a frame image corresponding to the timing at which the ventricle changes from diastole to systole in the cardiac cycle. In the template of the frame image corresponding to the timing when the ventricle changes from the systole to the diastole in the cardiac cycle, information indicating that is written.

  Next, 1 is set to the counter n (step 302), and the warping process of the frame image whose imaging order is (n + 1) is executed (step S303).

  The warping process is performed as follows, for example.

  First, the shift values (Δx, Δy) of the center point (center pixel) of each small region A1 of the frame image of the nth frame image and the corresponding center point of each small region A1 of the (n + 1) th frame image are respectively set. Calculated. The small area A1 is an area obtained in step S103 or step S105 of the area dividing process, and each shift value (Δx, Δy) is set to the center point of each small area A1 of the nth frame image (x, y ), Where (x ′, y ′) is the center point of each corresponding small region A1 of the (n + 1) th frame image, (Δx = x′−x, Δy = y′−y) is calculated. Desired.

  Next, a shift value (Δx, Δy) for each pixel of the (n + 1) th frame image is calculated by an approximation process using a two-dimensional 10th order polynomial using the obtained shift values (Δx, Δy). Then, based on the obtained shift value (Δx, Δy) of each pixel, nonlinear distortion conversion processing (warping processing) is performed on the (n + 1) th frame image, and each pixel of the (n + 1) th frame image is A new shifted frame image is created separately from the frame image before the warping process. The correspondence relationship of each pixel before and after the warping process in each frame image is stored in the RAM. Thereby, it is possible to determine which pixel before the warping process corresponds to each pixel after the warping process (which small area A2 includes). The new frame image obtained by the warping process is an image with very good matching at the corresponding pixel with the nth frame image. By performing the warping process, the shape in the lung field between the frame images can be matched with the reference image P1.

  Next, it is determined whether or not (n + 1)> the number of frame images. If it is determined that (n + 1)> the number of frame images is not satisfied (step S304; NO), the counter n is incremented by 1 (step S305). The process returns to step S303. If it is determined that (n + 1)> the number of frame images (step S304; YES), the process proceeds to step S306.

  In step S306, a series of frame images are grouped in units of cardiac cycles (for each identical identification number assigned in step S301). Next, 1 is set to the counter n (step S307), and the corresponding pixel values of each frame image created by the warping process in the group of number n are added, and further divided by the number of frame images belonging to the number n. Thus, an averaged image is created (step S308). Next, a blood vessel region is extracted from the created averaged image (step S309).

  The extraction of the blood vessel region in the averaged image in step S308 is, for example, a method of extracting a linear structure using the maximum eigenvalue calculated from each pixel of the Hessian matrix (for “circular / linear pattern detection in medical images”). No. 1pp175-185) of IEICE Transactions Journal D-II Vol.J87-D-II No.1pp175-185) can be applied. Further, by constructing a band division filter bank that generates each element of the Hessian matrix, it is possible to extract a linear structure at each resolution level, and it is possible to extract blood vessel regions having different sizes. In this method, the ribs are extracted simultaneously with the blood vessel shadow, but as described above, the ribs are recognized by using the rib shape model and deleted from the extraction result. Furthermore, for the extraction of peripheral blood vessels, for example, a dendritic figure model that can be deformed such as stretching, merging, and dividing considering the shape of the blood vessel shadow is used as a model of the blood vessel structure. Extracting blood vessel regions can be extracted by using the method for extracting the blood vessel ("Automatic extraction procedure of blood vessel shadow from chest X-ray image using Deformable Model" MEDICAL IMAGENG TECHNOLOGY Vol.17 No.5 September 1999) .

  Next, the concentration change amount of each pixel on the extracted blood vessel region is calculated and analyzed, and it is determined whether or not the blood flow state of each small region A2 is abnormal (step S310).

  For example, a frame image of a predetermined period (from the timing when the ventricle changes from the diastole to the systole to the timing when the ventricle changes from the systole to the diastole) is extracted from the warped frame image for one cardiac cycle, and the standard determined from that is extracted. A difference image is calculated by taking a difference between signal values (density values) between corresponding pixels of the image P2 (here, a frame image at a timing when the ventricle changes from diastole to systole) and each frame image. Thus, the density change amount of each pixel is calculated. Then, in each pixel on each blood vessel region extracted in step S309, the integrated value of the density change amount in a predetermined period is set to a reference value determined in advance according to imaging conditions (for example, tube voltage) / blood vessel diameter. If the comparison exceeds a predetermined reference value ± α, the blood flow state of the small area A2 including the pixel is determined to be abnormal. The blood vessel diameter in each image can be obtained based on the number of pixels between the ends of the width of the extracted blood vessel region. The reference value may be changed according to patient information (patient height, weight, age, sex).

  Further, the density change timing in each pixel on each blood vessel region (the timing at which the density change amount from the reference image P2 in the cardiac cycle becomes equal to or greater than a predetermined value corresponding to the imaging condition / blood vessel diameter) and the heart The normal value (standard value) of the concentration change timing according to the distance / blood vessel diameter is compared, and if the normal value exceeds a predetermined range (for example, normal value ± 20%), the pixel is included The blood flow in the small area A2 is determined to be abnormal. This normal value is a function of the distance from the heart. This normal value is determined by patient information (age, height, sex) and imaging information (normal / deep breathing). In comparison with the normal value, the measurement data (timing at which the density change amount from the reference image P2 becomes equal to or greater than the predetermined value) is normalized so that the normal value and the cardiac cycle coincide with each other (the density from the reference image P2). Comparison may be made after calculating the timing at which the amount of change is equal to or greater than a predetermined value / cardiac cycle at the time of capturing a frame image × cardiac cycle of a normal value.

  If there is a small area A2 determined to be abnormal, information indicating the type of abnormality (for example, a code indicating “blood flow: concentration change” or “blood” in the header area of the reference image P2 in each cardiac cycle unit, etc. Flow: code indicating “concentration change timing”) and position information (for example, coordinates of four vertices of the small area A2) of the small area A2 determined to be abnormal are written in association with each other.

  Here, an averaged image is created to extract a blood vessel region, and an abnormality in the blood flow state of each small region A2 is determined from the density change of each pixel on the blood vessel region, but the blood vessel region is not extracted, It is also possible to simply calculate an average signal value in the small area A2 of the cardiac cycle unit and use the fluctuation of the average signal value as an index of blood flow. For example, normality / abnormality of the blood flow state is determined based on the difference in the signal value change amount from the surrounding small area and the shift in the signal value change timing.

  It is also possible to determine normality / abnormality of the blood flow state by measuring / analyzing not only the concentration change but also the blood vessel diameter. For example, a method of calculating the maximum blood vessel diameter in a predetermined region using a Gaussian Hessian matrix and comparing the obtained values in the vertical direction of the lung field (“maximum blood vessel diameter ratio in upper and lower lung fields from chest X-ray images” By using "MEDICAL IMAGENG TECHNOLOGY Vol.19 No.5 September 1999)", normal / abnormal blood flow can be determined. In addition, it is possible to determine normality / abnormality of blood flow by combining analysis based on concentration change and analysis based on blood vessel diameter.

  When the analysis and determination in the group of number n is completed, it is determined whether n> (number of cardiac cycle units) or not, and it is determined that n> (number of cardiac cycle units) is not satisfied (step S311; NO), the counter n is incremented by 1 (step S312), and the process returns to step S307. If it is determined that n> (number of cardiac cycle units) (step S311; YES), the results of cardiac cycle units are integrated (step S313). For example, the small area A2 determined to be abnormal in at least one cardiac cycle unit is determined to be abnormal, and the integrated determination result is written in, for example, the reference image P2 (frame image with the imaging order of 1). Then, this process ends, and the process proceeds to step S14 in FIG.

  In step S14 of FIG. 3, an abnormality determination process is executed. Specifically, for each small region A2 in the series of frame images, the determination result by the arousal determination process and the determination result by the blood flow determination process are collated, and the determination result by the arousal determination process and the determination by the blood flow determination process Based on the combination of results, it is finally determined whether or not each small area A2 is abnormal. For example, the small region A2 determined as “no abnormality” in the arousal determination process and determined as “the change in blood flow concentration is smaller than a threshold value and abnormal” in the blood flow determination process is suspected of chronic lung type. It is determined that the region is abnormal. Also, in the arousal determination process, it is determined that “the area change is smaller than the surrounding area” or “the area change is small compared to the paired lung field region”, and the small area that is determined as “no abnormality” in the blood flow determination process. A2 is determined to be an abnormal region suspected of having chronic bronchitis.

  The final determination result, specifically, the positional information (for example, the four vertices of the small region A2) of the small region A2 finally determined to be abnormal by the combination of the determination result of the aspiration determination processing and the determination result of the blood flow determination processing ), Disease name, etc. are written in the header information of each frame image.

  When the abnormality determination process ends, a series of input image data (frame images) is transmitted to the image server 5 via the communication unit 43 (step S15), and this process ends.

In the image server 5, when a series of image data of a dynamic image is received from the arithmetic unit 4, the received series of image data is stored in a storage device.
(Operation of diagnostic console 3)
Next, the operation in the diagnostic console 3 will be described.

  In the diagnostic console 3, when the identification ID of the dynamic image to be displayed is input by the operation unit 33 and an image display is instructed, the control unit 31 and the display control processing program stored in the storage unit 32 are used. The display control process shown in FIG. 10 is executed by cooperation.

  First, an acquisition request for a series of image data (frame images) of a dynamic image having an identification ID input to the image server 5 is transmitted via the communication unit 35, and a series of dynamic images to be displayed is displayed from the image server 5. Image data (frame image) is acquired (step S21).

  Next, the arousal determination result, blood flow determination result, and final determination result attached to the header area of each frame image are acquired (step S22), and the acquired aspiration determination result, blood flow determination result, and final determination result are acquired. Based on this, the determination result display screen is displayed on the display unit 34 (step S23), and this process ends.

  FIG. 11A shows an example of the determination result display screen 341 displayed on the display unit 34 in step S23. As shown in FIG. 11A, the determination result display screen 341 displays an arousal determination result display area 341a for displaying an arousal determination result, a blood flow determination result display area 341b for displaying a blood flow determination result, and a final determination result. The final determination result display area 341c is displayed, and the arousal determination result, the blood flow determination result, and the final determination result are displayed on one screen.

  In step S23, first, based on the arousal determination result, the blood flow determination result, and the final determination result acquired from each frame image, the small area A2 determined to be abnormal by the aspiration determination process, and determined to be abnormal by the blood flow determination process The small area A2 and the small area A2 finally determined to be abnormal by the abnormality determination process are extracted. Here, the small area A2 determined to be abnormal in any one of the series of frame images is extracted. Next, the reference image P1 on which the small area A2 is drawn is displayed in each of the arousal determination result display area 341a, the blood flow determination result display area 341b, and the final determination result display area 341c, and the arousal determination result display area 341a. An annotation indicating the small area A2 determined to be abnormal in the arousal determination process is superimposed on the displayed reference image P1, and abnormal in the blood flow determination process on the reference image P1 displayed in the blood flow determination result display area 341b. An annotation indicating the small area A2 determined to be superimposed is displayed, and an annotation indicating the small area A2 determined to be abnormal in the abnormality determination process is superimposed and displayed on the reference image P1 displayed in the final determination result display area 341c. . As an annotation display method, for example, as shown in W1 and W2 in FIG. 11A, a small area A2 determined to be abnormal is displayed with a thick frame. Moreover, you may make it display by changing a color. Furthermore, in the small area A2 determined to be abnormal, the doctor can confirm the degree of abnormality by changing the color of the thick frame and the display according to the number of frame images in which the small area A2 is determined to be abnormal. Good.

  Note that the determination result display screen 341 is not limited to the screen shown in FIG. For example, when transmitting a series of frame images from the arithmetic device 4 to the diagnostic console 3, the averaged image and the blood vessel extraction result in the averaged image are also transmitted, and the blood flow determination result region 341b As shown in FIG. 11B, an annotation may be displayed in the small area A2 determined to be abnormal on the averaged image in which the extracted blood vessels are emphasized.

  In addition, as another example of the determination result display screen 341, a series of frame images of dynamic images are sequentially switched in the shooting order in each of the arousal determination result display area 341a, the blood flow determination result display area 341b, and the final determination result display area 341c. By displaying the dynamic image, the dynamic image is displayed, and at the time of displaying each frame image, the annotation is displayed in the small area A2 determined to be abnormal in the frame image, thereby notifying the doctor of the timing of the abnormality. You may do it.

  Moreover, in the determination result display screen 341, in order to show the basis of the final determination result, the arousal determination result and the blood flow determination result are displayed together. However, at least the final determination result may be displayed. In the abnormality determination result, it is preferable to display the disease name determined to be suspicious.

  Further, as another example of the determination result display screen 341, for example, on one reference image P1, both aeration and blood flow are normal, only aspiration is abnormal, only blood flow is abnormal, both aeration and blood flow are abnormal, These locations may be displayed in different colors.

  As described above, according to the dynamic image diagnosis support system 100 according to the present invention, the arithmetic device 4 divides each of the plurality of frame images of the chest dynamic image captured by the imaging device 1 into a plurality of small regions. The image analysis is performed for each corresponding small region between a plurality of frame images, and the arousal determination process for determining whether or not the aspiration state of each small region is abnormal, the blood flow state of each small region is abnormal A blood flow determination process for determining whether or not there is present, and an abnormality determination process for determining whether or not each small region is abnormal based on the determination result by the arousal determination process and the determination result by the blood flow determination process . The diagnosis console 3 displays at least the determination result in the abnormality determination process.

  Therefore, it is possible to provide diagnosis support information that takes into consideration not only the state of arousal but also the state of blood flow accompanying respiration.

  When blood flow is determined, warping processing is performed on a plurality of frame images to match the shape of the lung field region between the plurality of frame images, and then the blood vessel region is extracted. It is not necessary for the patient to hold his or her breath when taking a picture in order to match each frame.

  Further, since the annotation is displayed in the small area on the reference image P1 determined to be abnormal in the abnormality determination process on the determination result display screen, the doctor can easily recognize the portion determined to be abnormal. Become.

  In addition, as a display method of the determination result display screen, the doctor easily recognizes the timing determined to be abnormal by displaying the annotation in the small area determined to be abnormal by the abnormality determination processing in each frame image displayed as a moving image. It becomes possible.

  In addition, the description in this Embodiment mentioned above is an example of the suitable dynamic image diagnosis assistance system which concerns on this invention, and is not limited to this.

  For example, when an annotation of an abnormal part is displayed on the moving image display on the determination result display screen, the abnormal part determined in cardiac cycle units may be displayed as the blood flow determination result.

  For example, in the above description, an example in which a hard disk, a semiconductor non-volatile memory, or the like is used as a computer-readable medium of the program according to the present invention is 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 program data according to the present invention via a communication line.

  In addition, the detailed configuration and detailed operation of each device constituting the dynamic image diagnosis support system 100 can be changed as appropriate without departing from the spirit of the present invention.

DESCRIPTION OF SYMBOLS 100 Dynamic image diagnosis support system 1 Imaging device 11 Radiation source 12 Radiation irradiation control device 13 Radiation detection unit 14 Reading control device 15 Cycle detection sensor 16 Cycle detection device 2 Imaging console 21 Control unit 22 Storage unit 23 Operation unit 24 Display unit 25 Communication unit 26 Bus 3 Diagnosis console 31 Control unit 32 Storage unit 33 Operation unit 34 Display unit 35 Communication unit 36 Bus 4 Arithmetic device 41 Control unit 42 Storage unit 43 Communication unit 44 Bus 5 Image server

Claims (2)

A reference image is defined from a plurality of frame images showing the dynamics of the chest obtained by dynamic imaging of the human chest, and the reference image is divided into a plurality of small regions. Area dividing means for calculating small areas corresponding to a plurality of small areas of the reference image in frame images other than the reference image,
An analysis unit that performs image analysis for each corresponding small area in the plurality of frame images, and obtains ventilation state information for each small area;
With
Said analyzing means, before SL for each small area, dynamic image analyzer, characterized in that the area change relative to the reference image to obtain a timing which exceeds a predetermined value as the information of the ventilation. The dynamic image analysis apparatus according to claim 1, wherein the analysis unit determines that an area in which the timing acquired for each small area exceeds a predetermined value is abnormal .

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