JP2009153678A - Kinetic image processing system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a kinetic image processing system to provide data effective for the diagnosis of the ventilation capacity of the lung. <P>SOLUTION: The breast part of a subject is subjected to kinetic photographing by a photographing apparatus to form kinetic images in a plurality of time phases with respect to at least one respiration phase while the data of absolute ventilation quantity is acquired by the image analyzing part of an image processor (Step S13) and estimated change quantity per unit signal change quantity is calculated from the total signal change quantity and absolute ventilation quantity of the kinetic images between the maximum respiration phase and the maximum expiration phase (Step S14). Further, an image analyzing part uses the value of the estimated change quantity per the unit signal change quantity to calculate the estimated ventilation quantity in each of the time phases from the change quantity of a signal value between the kinetic images of the maximum respiration phase and the maximum expiration phase and the kinetic images of another time phase (Step S16). In a diagnostic console, the calculated estimated ventilation quantity is displayed on a display part by a control part. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a dynamic image processing system.

  Conventionally, an apparatus for analyzing an X-ray image or the like and detecting an image region estimated to be a lesion is disclosed (for example, see Patent Document 1). In order to provide information so that a doctor can observe an X-ray image or the like to determine whether it is abnormal or normal, in such an apparatus, a candidate area of a lesion part detected in an X-ray image or the like is provided. The indication which points is done.

Also disclosed is a method of quantifying a concentration change by graphing the concentration distribution and displaying it as information necessary for diagnosis (for example, see Patent Document 2). In general, a lesion has a density change compared to a normal tissue part, and diagnosis support is provided by providing information on such a density change to a doctor.
JP-A-7-37061

  However, with regard to lung ventilation, not only local lesions that cause functional decline but also findings such as ventilation volume may be important for diagnosis. Therefore, it cannot be said that the conventional method of detecting and displaying only the lesioned part can provide sufficient diagnosis support for the ventilation ability.

  An object of the present invention is to provide information effective for diagnosis of lung ventilation ability.

According to the invention of claim 1,
Imaging means for dynamically imaging the chest of a subject and generating dynamic images at a plurality of time phases for at least one respiratory phase;
Information on the absolute ventilation volume between the maximum expiratory position and the maximum inspiratory position in the respiratory phase is obtained, and a signal between the absolute expiratory volume and the dynamic image of the maximum expiratory position and the maximum inspiratory position among the generated dynamic images. An image analysis means for calculating an estimated ventilation volume per unit signal change amount from a change amount of the value, and calculating an estimated ventilation volume in each time phase using the estimated ventilation volume value per unit signal value;
Display means;
Control means for displaying the estimated ventilation volume calculated for each time phase on the display means;
A dynamic image processing system is provided.

According to invention of Claim 2,
The dynamic image processing system according to claim 1, wherein the control unit displays a numerical value indicating the calculated estimated ventilation amount.

According to invention of Claim 3,
3. The control unit according to claim 1, wherein the control unit generates an image image indicating the calculated estimated ventilation amount in a lung field region of each dynamic image, and continuously displays the image image according to a time phase. The described dynamic image processing system is provided.

According to invention of Claim 4,
The image analysis means divides a lung field region included in the dynamic image into a plurality of regions, calculates the estimated ventilation for each of the divided regions,
The dynamic image processing system according to any one of claims 1 to 3, wherein the control unit displays an estimated ventilation amount calculated for each of the divided regions in the dynamic image.

  According to the first aspect of the present invention, it is possible to provide information on the estimated ventilation volume at each time phase when a dynamic image is taken. When observing a dynamic image and diagnosing ventilation capacity, a doctor can use information on the estimated ventilation volume as effective reference information.

  According to the second aspect of the present invention, the estimated ventilation volume can be grasped from specific numerical values.

  According to invention of Claim 3, the change of the estimated ventilation volume with progress of time can be grasped | ascertained visually.

  According to the invention described in claim 4, it is possible to grasp the estimated ventilation amount that changes for each region. Since the measuring device can only measure the ventilation volume of the entire lung, information on the estimated ventilation volume for each area is particularly effective when making a diagnosis by paying attention to the area where the ventilation capacity is reduced.

First, the configuration will be described.
FIG. 1 shows a dynamic image processing system 1 in the present embodiment.
As illustrated in FIG. 1, the dynamic image processing system 1 includes an imaging device 10, an imaging console 20, a diagnostic console 30, an image processing device 40, and a server 50. The constituent devices 10 to 50 are connected via a network N.

  With reference to FIG. 2, the imaging device 10, the imaging console 20, and the diagnostic console 30 will be further described. The imaging apparatus 10 includes an X-ray source 11, a detector 12, a reading unit 13, and a cycle detection unit 14. On the other hand, the imaging console 20 includes a control unit 21, a storage unit 22, an operation unit 23, a display unit 24, and a communication unit 25. Similarly, the diagnostic console 30 includes a control unit 31, a storage unit 32, an operation unit 33, a display unit 34, and a communication unit 35.

First, the imaging device 10 will be described.
The imaging apparatus 10 irradiates the subject W with X-rays and reads an X-ray image from the detector 12. The photographing apparatus 10 can perform dynamic photographing. A dynamic image is an imaging method in which imaging is performed continuously to obtain dynamic images at a plurality of time phases. The dynamic image refers to a captured image obtained by dynamic imaging, and in this embodiment, the dynamic image is an X-ray image.

  The X-ray source 11 emits X-rays according to the control of the control unit 21 of the imaging console 20. Examples of controlled X-ray irradiation conditions include pulse rate, pulse width, pulse interval, irradiation start / end timing, X-ray tube current, X-ray tube voltage, filter value, and the like during continuous imaging in dynamic imaging. The pulse rate is the number of shots per unit time. The pulse width is the X-ray irradiation time per imaging. The pulse interval is the time from the start of X-ray irradiation in continuous imaging until the start of X-ray irradiation in the next imaging.

  The detector 12 is disposed at a position facing the X-ray source 11 with the subject W interposed therebetween. The detector 12 is an FPD (Flat Panel Detector) or the like in which X-ray detection sensors are arranged in a matrix. That is, X-rays are converted into electrical signals corresponding to the intensity and stored for each pixel (detection sensor), so that an X-ray image is recorded on the detector 12.

  The reading unit 13 performs processing for reading an X-ray image from the detector 12, and transmits the read X-ray image to the imaging console 20. The reading operation is controlled by the control unit 21. The image reading conditions to be controlled include a frame rate, a frame interval, a pixel size, and the like. The frame rate and the frame interval are the same as the pulse rate and the pulse interval.

The cycle detection unit 14 detects a cycle of the biological reaction for the imaging region of the subject W. For example, when the imaging region is the chest including the lung, a respiratory cycle is detected by applying a respiratory monitor belt, a CCD camera, an optical camera, a spirometer, or the like. When the imaging region is the heart, the heartbeat cycle is detected using a heartbeat meter, an electrocardiograph or the like.
The cycle detection unit 14 outputs the detected cycle information to the control unit 21 of the imaging console 20.

Next, the imaging console 20 and the diagnostic console 30 will be described.
The imaging console 20 is used for an imaging operation of the engineer, and receives an input of imaging conditions and displays an X-ray image of the imaging apparatus 10 for the engineer's confirmation. The diagnostic console 30 is used for a doctor's operation, and displays an X-ray image transmitted from the imaging console 20 for a doctor's confirmation.

  The functions of each part of the diagnostic console 30 (the control unit 31, the storage unit 32, the operation unit 33, the display unit 34, and the communication unit 35) are the same as those of the imaging console 20 (the control unit 21, the storage unit 22, the operation unit 23, The display unit 24 and the communication unit 25) are basically the same. Therefore, here, each part of the imaging console 20 will be described as a representative, and description of each part of the diagnostic console 30 will be omitted.

The control unit 21 includes a CPU (Central Processing Unit), a RAM (Random Access Memory), and the like. The control unit 21 reads various programs stored in the storage unit 22 by the CPU, expands them in the RAM, performs various calculations in cooperation with the expanded programs, and centrally controls the operations of the respective units. Execute the process.
The control unit 21 has a timer function for measuring time using the CPU clock.

  The storage unit 22 is a memory such as a hard disk, and stores various programs used by the control unit 21 and parameters necessary for executing the programs. For example, the imaging conditions (such as X-ray irradiation conditions and X-ray image reading conditions) optimized for each imaging region are stored.

The operation unit 23 includes a keyboard, a mouse, and the like, generates an operation signal according to these operations, and outputs the operation signal to the control unit 21.
The display unit 24 includes a display, and displays various operation screens, X-ray images obtained by imaging, and the like according to display control of the control unit 21.
The communication unit 25 includes a communication interface, and communicates with an external device connected to the network N.

Next, the image processing apparatus 40 and the server 50 will be described.
The image processing device 40 and the server 50 are used to provide an X-ray image obtained by imaging.
The image processing apparatus 40 will be described with reference to FIG.
The image processing apparatus 40 performs image processing on an X-ray image so that the image quality is easy for a doctor to observe. As shown in FIG. 3, the image processing apparatus 40 includes a control unit 41, an operation unit 42, a display unit 43, a storage unit 44, a communication unit 45, an image processing unit 46, and an image analysis unit 47.

  Since the basic functions of the control unit 41 to the communication unit 45 are the same as those of the control unit 21 to the communication unit 25 of the imaging console 20 described above, detailed description thereof is omitted here.

  The image processing unit 46 performs various image processing such as gradation conversion processing and frequency adjustment processing on the X-ray image. The image processing is performed according to the image processing conditions corresponding to the imaging region, depending on the type corresponding to the imaging region.

  The image analysis unit 47 analyzes dynamic images at a plurality of time phases obtained by dynamic imaging of the chest, and calculates an estimated ventilation volume at each time phase. A specific calculation method will be described later.

  The server 50 includes a large-capacity memory, and stores and manages the X-ray image processed by the image processing apparatus 40 in this memory. The X-ray image stored in the server 50 is distributed in response to a request from the diagnostic console 30 and used for diagnosis.

Next, the operation will be described.
The dynamic image processing system 1 according to the present embodiment performs dynamic imaging of the chest, performs image analysis using the obtained dynamic images at a plurality of time phases, and calculates and displays an estimated ventilation volume at each time phase.
FIG. 4 is a flowchart showing the flow of processing in the imaging device 10, the diagnostic console 30, and the image processing device 40 that mainly function at that time.

As shown in FIG. 4, first, dynamic imaging is performed by the imaging device 10 to generate dynamic images at a plurality of time phases (step S1). The dynamic imaging is performed so as to generate a dynamic image having a plurality of temporal phases for at least one respiratory phase.
At the time of imaging, the imaging engineer inputs patient information regarding the subject W, specifies an imaging region, and the like via the operation unit 23 of the imaging console 20. In addition to the subject W, that is, the patient's name, the patient information includes information indicating patient attributes such as age, sex, weight, and height.

In the imaging console 20, an imaging condition corresponding to an imaging region designated by the control unit 21 is read from the storage unit 22 and set as an X-ray irradiation condition in the X-ray source 11 of the imaging apparatus 10 and an image reading condition in the reading unit 13. To do. In the following description, it is assumed that the imaging region of “lung (ventilation)” is designated by the imaging technician. When the lungs are imaged to see the ventilation capacity, the respiratory cycle is about 0.3 times / second on average, so that it is possible to capture dynamic images of multiple time phases for at least one respiratory phase. For example, the following shooting conditions are set.
Frame rate (pulse rate): 2 frames / second (that is, 3 shots per second)
Pixel size: 400μm
Image size: 40cm x 30cm
Tube voltage: 120 kV
Tube current: 50 mA
Shooting timing: Every frame interval from the timing of the conversion point from inspiration to expiration (shooting start timing)

  The control unit 21 corrects conditions such as a frame rate based on the information on the respiratory cycle detected by the cycle detection unit 14. For example, based on the detected respiratory cycle, the control unit 21 calculates and resets the frame rate so that one respiratory phase is imaged with a predetermined number of frames (for example, 10 frames). In the above example of the frame rate condition, when the number of respiratory cycles detected by the cycle detection unit 14 is 0.25 times / second, the frame rate is corrected to 2.5 frames / second.

  After setting the imaging conditions, the control unit 21 determines whether it is imaging start timing, that is, timing when one respiratory phase starts (for example, a conversion point of inspiration → expiration) based on the information of the respiratory cycle detected by the cycle detection unit 14. Determine whether or not. At the imaging start timing, the control unit 21 controls the X-ray source 11 and the reading unit 13 to start dynamic imaging. In addition, the control unit 21 passes the shooting time required from the start to the end of shooting in accordance with the start of dynamic shooting.

  The imaging apparatus 10 emits X-rays at a predetermined pulse rate according to the set X-ray irradiation conditions. Similarly, the reading unit 13 performs X-ray image reading processing from the detector 12 at a predetermined frame rate in accordance with the set image reading conditions. The control unit 21 synchronizes the X-ray irradiation operation and the image reading operation. Thereby, dynamic images in a plurality of time phases are generated and output to the imaging console 20.

  In the imaging console 20, a dynamic image of each time phase obtained by dynamic imaging by display control of the control unit 21 is displayed on the display unit 24. This is because the photographer confirms the image quality and the like. When an approval operation is performed by the imaging engineer via the operation unit 23, the control unit 21 performs diagnosis by attaching an ID for identifying a series of imaging, patient information, and imaging time information to the dynamic image of each time phase. To the console 30. In the same manner, the diagnostic console 30 also displays a confirmation display (step S2). When an approval operation is performed, a dynamic image of each time phase is transmitted to the image processing device 40.

  In the image processing device 40, the image processing unit 46 performs image processing corresponding to the imaging region of the lung (ventilation) on the dynamic image of each time phase, and then the image analysis unit 47 calculates the estimated ventilation volume for each dynamic image. A calculation process is performed (step S3).

Ventilation volume refers to the amount of air that changes between the maximum expiratory position (phase when fully exhausted) and the maximum inspiratory position (phase when fully inhaled) shown in FIG. In particular, in the expiration phase, the amount of exhalation exhausted from the maximum expiration position to the maximum inspiration position, and in the inspiration phase, the intake amount inhaled between the maximum expiration position and the maximum inspiration position.
During breathing, the lung volume changes as the respiratory phase changes due to the stretching motion of the lower lung. It can be said that the ventilation volume is substantially equal to the lung volume of the expansion / contraction part, that is, the volume of the lung part expanding and contracting between the maximum expiratory position and the maximum inspiratory position.

Lung volume changes mainly when the lower part of the lung expands and contracts up and down, so it is assumed that the stretched lung part is a cube with the bottom of the lung as the bottom, and multiplying the area of the stretched lung part and the lung thickness The volume of the lung portion can be determined. That is, as shown in FIG. 5, the length of the lung bottom of the lung imaged from the front direction is a, the length of the lung portion expanded and contracted with reference to the position of the lung bottom imaged from the front direction is Δh, and from the side surface When the photographed lung thickness is b, the volume V of the lung portion that expands and contracts between the maximum expiratory position and the maximum inspiratory position can be obtained by the following equation 1. The length a, Δh, and thickness b are obtained by counting pixels.
V = a × b × Δh (1)

The volume V can also be obtained by the following method.
A histogram of signal values is obtained using an X-ray image taken from the front. Since a peak region indicating a lung field region appears in the histogram, pixels having a signal value corresponding to the peak region of the lung field region are counted. This is performed for each of the maximum expiratory position and the maximum inspiratory position, and the difference between them is obtained. Since this difference corresponds to the area of the lung portion expanded and contracted between the maximum expiratory position and the maximum inspiratory position in the X-ray image captured from the front, the volume V is obtained by multiplying the difference by the lung thickness b captured from the side. be able to.

  On the other hand, the signal value of the X-ray image is determined by the X-ray transmission amount of the subject W, and the X-ray transmission amount changes depending on the thickness of the subject W. This is because the greater the thickness of the subject W, the more difficult it is to transmit X-rays. Therefore, the signal value of the X-ray image is one index representing the lung bottom thickness of the subject W. If the signal value changes, the thickness changes, that is, the volume V (ventilation volume) of the lung portion. You can think that it is changing. In the present embodiment, the relationship between the signal value of the dynamic image and the ventilation amount is quantified, and the estimated ventilation amount in the time phase of each dynamic image is obtained using the quantified value.

The process for calculating the estimated ventilation volume will be described with reference to FIG.
As shown in FIG. 6, the image analysis unit 47 determines a respiratory phase for each dynamic image in a plurality of time phases (step S11). Since the lower lung contracts during expiration and the lower lung expands during inspiration, the image analysis unit 47 calculates the area (number of pixels) of the lung field region of the dynamic image related to each time phase, and the time when this area becomes maximum A dynamic image from the phase to the minimum time phase is determined as the expiration phase, and a dynamic image from the minimum time phase to the maximum time phase is determined as the inspiration phase. Figure 7 shows the results of determining the respiratory phase for the dynamic image of each time phase _{T (T = t 0 ~t 6} ).

  Note that any method may be applied to recognize the lung field region. For example, a threshold value is obtained by discriminant analysis from the histogram of the signal value of the reference image, and a region having a higher signal than the threshold value is defined as 1 Next detect. Next, edge detection is performed in the vicinity of the boundary of the first detected region, and a point in the edge in the small region near the boundary is extracted along the boundary, so that the boundary of the lung field region can be detected.

  Next, the image analysis unit 47 determines that the dynamic image having the maximum lung field area is the dynamic image at the maximum inspiratory position and the dynamic image having the minimum area is the dynamic image at the maximum expiratory position. Then, a signal amount that changes between the maximum inspiratory position and the maximum expiratory position (hereinafter referred to as a total signal change amount) is calculated from the difference in the signal distribution of each dynamic image (step S12).

The signal amount can be obtained by creating a histogram of the dynamic image.
FIG. 8A is a diagram showing a dynamic image ga at the maximum expiratory position and a histogram ha of the signal values. FIG. 8B is a diagram showing a dynamic image gi at the maximum inspiratory position and a histogram hi of the signal values. Three peaks appear roughly in the histograms ha and hi. Appearing in the high signal region is a direct X-ray region in which X-rays are directly detected without passing through the subject W, and appearing on the low signal side is a trunk region such as a heart or bone having low X-ray transmittance. It is. Appearing between them is a lung field region that penetrates the lungs.

  The amount of signal in the lung field area of each dynamic image ga, gi corresponds to the area of the signal distribution in the lung field area. That is, it can be obtained by multiplying the signal value constituting the signal distribution of the lung field region by the frequency. Since the area of the lung field area is larger at the maximum inspiratory position, the area of the signal distribution of the lung field area is larger in the histogram hi shown in FIG. 8B than in the lung field area in the histogram ha shown in FIG. It turns out that there is much signal amount.

  The image analysis unit 47 detects the signal distribution of the lung field region in the histograms ha and hi, and calculates the difference in the signal distribution of each lung field region as shown in FIG. For the signal distribution that is the calculated difference, the signal amount obtained by multiplying the distributed signal value by the frequency is the signal amount that has changed between the maximum expiratory position and the maximum inspiratory position, that is, the total signal change amount.

  Next, the image analysis unit 47 acquires information on absolute ventilation corresponding to the total signal change amount (step S13). The absolute ventilation volume is a measured value of the ventilation volume or a value that can be said to be substantially the same as the measured value, and is distinguished from an estimated ventilation volume estimated by a calculation described later. The absolute ventilation volume information may be obtained by acquiring an actual measurement value of a ventilation volume (tidal volume, forced vital capacity, etc.) measured by a spirometer by connecting a spirometer or by an input operation of an engineer. Alternatively, as shown in FIG. 6, the subject W is dynamically photographed from the front and the side, the lung bottom is detected from the dynamic images of the maximum expiratory position and the maximum inspiratory position, and Δh is obtained from the difference between the positions of the lung bottom, It is good also as calculating | requiring the volume V by calculating | requiring the length a and thickness b of a bottom, and acquiring as absolute ventilation. The volume V is not an actual measurement value, but can be used as a value that is substantially the same as the actual measurement value.

  Next, the image analysis unit 47 assumes that the signal change has occurred by the total signal change amount due to the ventilation (inspiration or exhalation) by the absolute ventilation amount, and the total signal change amount and the acquired ventilation amount Associate. Then, from the total signal change amount and the absolute ventilation amount, a ventilation amount estimated to change when the signal value changes by 1, that is, an estimated ventilation amount per unit signal change amount is calculated (step S14).

  The estimated ventilation volume per unit signal variation is obtained by dividing the absolute ventilation volume by the total signal variation. For example, when the acquired absolute ventilation amount is 5000 cc and the total signal change amount is 10,000, the estimated ventilation amount per unit signal change amount is 5000/10000 = 0.5. That is, when the signal value changes by 1, it can be estimated that the ventilation amount has changed by 0.5 cc.

  Next, the image analysis unit 47 calculates the difference in signal distribution in the lung field of the dynamic image belonging to the inspiratory phase with reference to the dynamic image at the maximum expiratory level. Similarly, using the dynamic image at the maximum inspiratory position as a reference, the difference in signal distribution in the lung field region of the dynamic image belonging to the expiration phase is calculated. Then, by determining the area of the signal distribution corresponding to the calculated difference (signal value × frequency), the amount of change in the signal value of the lung field region from the maximum expiratory position and the maximum inspiratory position in each time phase of the inspiratory phase and expiratory phase Is obtained (step S15).

When the change amount of the signal value in each time phase is obtained, the image analysis unit 47 uses the estimated ventilation amount value per unit signal change amount to estimate the estimated ventilation amount estimated to have changed from the maximum inspiratory position or the maximum expiratory position. Is calculated (step S16). Explaining an example in which the estimated ventilation volume per unit signal change amount is 0.5 cc, for example, as shown in FIG. 7, the dynamic image of the time phase T = t ₂ belongs to the expiration phase, but the lung field region of the dynamic image Is changed by 3000 with respect to the dynamic image (time phase T = t ₀ ) of the maximum inspiratory position as a reference. In this case, the estimated ventilation volume at the time phase t2 is a value obtained by multiplying the change amount of the signal value by the estimated ventilation volume per unit signal change amount, 3000 × 0.5 = 1500 cc.

As described above, not only the estimated ventilation volume in the entire lung is calculated from the change in the signal amount of the entire lung field area, but also the lung field area is divided into a plurality of areas, and the estimated ventilation volume is calculated for each area. It is also possible.
For example, as shown in FIG. 10A, the lung field area is divided into three areas, and the signal distribution of the signal value is obtained for each of the areas A, B, and C as areas A, B, and C from above, and the area A is obtained by the method described above. , B, and C are calculated for the estimated ventilation volume. The lower the lungs, the greater the movement of expansion and contraction during breathing, and the lower the upper and lower the expansion and contraction. Therefore, as shown in FIG. 11, the signal change amount is the smallest in the upper region A and the lower region C is the largest in the regions A, B, and C. Thus, by calculating the estimated ventilation volume for each of the areas A to C, it is possible to capture changes in ventilation volume due to expansion and contraction.

  In calculating the estimated ventilation volume, the regions A to C need to be associated with each dynamic image, but this can be performed by local matching. Local matching is a method in which a certain dynamic image is used as a reference, and each divided region obtained by dividing the reference image is associated with a region having a high matching degree with another dynamic image. The degree of matching refers to the degree of image matching, and can be obtained by the least square method or cross-correlation.

  Further, as shown in FIG. 10B, the lung field region may be divided for each anatomical structure of the lung such as the upper right lobe and the upper left lobe, and the estimated ventilation volume may be calculated for each divided region. In this case, it is possible to capture a change in ventilation volume for each anatomical structure. At the time of division, a reference image in which the position and name of the anatomical structure are determined in advance is used to perform image processing such as nonlinear warping so that the lung field region of the reference image and the lung field region of each dynamic image substantially match. It is only necessary to recognize and divide each anatomical region by conversion.

  Next, the image analysis unit 47 attaches information on the estimated ventilation volume calculated for the dynamic image of the inspiration phase and the expiration phase to the dynamic image together with the information of the estimated ventilation volume per unit signal variation (step S17). . Thereafter, the dynamic image of each time phase accompanied by the estimated ventilation volume information is transmitted to the server 50 via the communication unit 44.

  The server 50 creates a database of dynamic images of each time phase together with the accompanying information and stores it in a memory. If there is a request from the diagnostic console 30, the server 50 transmits a dynamic image group of the patient related to the request.

As shown in FIG. 4, the diagnostic console 30 displays the dynamic image of each time phase acquired from the server 50 on the display unit 34 by the display control of the control unit 31 (step S4). At this time, the control unit 31 continuously switches each dynamic image according to the time phase and displays it as a moving image. The doctor can grasp the dynamic changes in the respiratory motion of the lungs.
Next, the control unit 31 displays information on the estimated ventilation volume on the display unit 34 based on the incidental information of the displayed dynamic image (step S5).

FIG. 12 shows a display example of a dynamic image and a display example of an estimated ventilation volume.
On the display screen d1 shown in FIG. 12, a dynamic image display area d11 and an estimated ventilation volume display area d12 are displayed. In the display area d11, the control unit 31 continuously switches and displays each dynamic image according to the time phase. On the other hand, in the estimated ventilation volume display area d12, the control unit 31 generates and displays an image diagram showing the estimated ventilation volume calculated in each dynamic image.

  The image diagram showing the estimated ventilation volume is obtained by coloring a pixel having a signal value used for calculation of the estimated ventilation volume in the dynamic image. In other words, if the dynamic image belongs to the expiratory phase, the pixels having signal values constituting the signal distribution corresponding to the difference from the dynamic image at the maximum inspiratory level are colored. A pixel having a signal value constituting a signal distribution corresponding to a difference from the dynamic image of the position is colored. The color differs depending on whether the ventilation volume is expiratory volume or inspiratory volume. Here, blue is used to indicate the expiratory volume in the dynamic image of the expiratory phase, and red is used to indicate the inspiratory volume in the dynamic image of the inspiratory phase. An example will be described.

FIG. 13A and FIG. 13B show examples of image diagrams showing estimated ventilation. FIG. 13A shows a case where the estimated ventilation volume is an expiration volume, and FIG. 13B shows a case where the estimated ventilation volume is an inspiration volume.
As shown in FIG. 13A, in the case of the expiratory phase, the expiratory amount of the dynamic image at the maximum inspiratory position (time phase T = t ₀ ) is set to 0, and each temporal phase T = t ₁ with reference to the dynamic image at the maximum inspiratory position. , T _2, t _{3 in} the dynamic image, the pixels related to the calculation of the estimated ventilation are given blue color. By adding blue color, it is possible to visually indicate the amount of expired air that has changed based on the dynamic image of the maximum inspiratory position.

The same applies to the intake phase. As shown in FIG. 13B, the inspiratory amount of the dynamic image (time phase T = t ₃ ) at the maximum expiratory position is set to 0, and the subsequent time phases T = t ₄ and t ₅ with reference to the dynamic image at the maximum inspiratory position. , T ₆ , the pixel whose estimated ventilation volume is calculated is colored red. This makes it possible to visually indicate the amount of inspiration that has changed with the dynamic image of the maximum expiratory position as a reference.

The control unit 31 displays an image diagram generated by performing coloring according to the estimated ventilation amount in each dynamic image on the display region d12 while continuously switching according to the time phase. The change in color in the image diagram makes it possible to visually grasp the change in estimated ventilation volume over time.
Note that the switching display is performed in accordance with the time phase of the original dynamic image in the display area d11. By linking the display of the original dynamic image and the dynamic state, it becomes possible to refer to information on the estimated ventilation volume while observing the original dynamic image.

  As the estimated ventilation volume is larger, more pixels are colored, so the color density in the image diagram is an index indicating the estimated ventilation volume. The control unit 31 displays an indicator d13 indicating how much ventilation the color density corresponds to, adjacent to the display area d12. In the indicator d13, 0 is displayed as the lower limit of the ventilation volume, and the value of the absolute ventilation volume (for example, 5000 cc or the like) is displayed as Max which is the upper limit.

  Furthermore, the control part 31 displays the estimated ventilation volume calculated about each dynamic image with a numerical value. Specifically, as shown in FIG. 12, a display area d14 for the estimated ventilation volume is provided at the bottom of the display area d12. In this display area d14, the control unit 31 displays the time of the image diagram currently displayed in the display area d12. Display the estimated ventilation volume corresponding to the phase.

  If there is a display instruction, information on the estimated ventilation volume calculated for each region may be displayed. In this case, an image diagram showing the estimated ventilation volume may be displayed as colored for each region, or the signal value change amount is replaced with the estimated change amount in the graph shown in FIG. The estimated ventilation volume at the inspiratory position may be set to 0, and the estimated ventilation volume at each time phase may be displayed as a graph with the inspiration phase and the expiration phase.

  As described above, according to the present embodiment, the imaging device 10 performs dynamic imaging of the chest of the subject W and generates dynamic images in a plurality of time phases for at least one respiratory phase. On the other hand, information on the absolute ventilation is acquired by the image analysis unit 47 of the image processing device 40, and an estimation per unit signal change from the total signal change and the absolute ventilation of the dynamic image between the maximum expiratory position and the maximum inspiratory position. The amount of change is calculated. Further, the image analysis unit 47 uses the estimated change amount value per unit signal change amount to calculate each signal value change amount between the dynamic image at the maximum expiratory position and the maximum inspiratory position and the dynamic image at another time phase. Calculate the estimated ventilation volume in the time phase. In the diagnostic console 30, the calculated estimated ventilation volume is displayed on the display unit 34 by the control unit 31, so that information on the estimated ventilation volume at each time phase can be provided to the doctor.

  In addition to displaying a numerical value indicating the estimated ventilation volume at the time of display, since the control unit 31 generates and displays an image diagram indicating the estimated ventilation volume, the doctor can grasp the estimated ventilation volume at each time phase with a specific numerical value. At the same time, it is possible to visually detect changes in the estimated ventilation volume with an image diagram.

  Further, when calculating and displaying the estimated ventilation volume for each area, the doctor can grasp the estimated ventilation volume changing for each area. The spirometer cannot measure the ventilation volume for each area, but only the information on the ventilation volume of the entire lung. Therefore, it provides diagnostically effective information when detecting areas with poor ventilation capacity. can do.

In addition, the said embodiment is a suitable example of this invention, and is not limited to this.
For example, in the above-described embodiment, the estimated ventilation volume is calculated by obtaining the difference in the signal distribution between the dynamic images whose temporal phases are adjacent to each other. However, the present invention is not limited to this. For example, in the expiratory phase, the estimated ventilation volume is calculated from the difference in signal distribution from the dynamic image based on the dynamic image at the maximum expiratory position as a reference. The estimated ventilation volume may be calculated from the difference in signal distribution with the dynamic image.

  Moreover, although the structure which displays the estimated ventilation volume in the diagnostic console 30 was demonstrated, it is good also as displaying on the imaging | photography console 20 and other apparatuses (PC etc. used for a diagnosis). Further, the configuration in which the image processing apparatus 40 for performing image analysis is provided and the estimated ventilation volume is calculated in the image processing apparatus 40 has been described. However, the diagnostic console 30 and other apparatuses install the program for calculating the estimated ventilation volume. The calculation may be performed.

  Further, as a computer-readable medium for storing the program related to the above-described processing, a portable type such as a DVD can be applied in addition to a memory such as a ROM. Also, a carrier wave can be used as a medium for providing female program data via a network.

It is a figure which shows the dynamic image processing system in this embodiment. It is a figure which shows the functional structure of the imaging device of FIG. 1, an imaging console, and a diagnostic console. It is a figure which shows the functional structure of the image processing apparatus of FIG. It is a figure which shows the flow of a process in a dynamic image processing system. It is a figure which shows the dynamic image of the maximum expiration position and the maximum inspiration among the dynamic images image | photographed from the front and the side. It is a figure explaining the flow of the process which calculates estimated ventilation. It is a figure which shows the dynamic image of several time phases. It is an example of the dynamic image of a maximum expiratory position, and the histogram of the signal value. It is an example of the dynamic image of the maximum inspiratory position and the histogram of the signal value. It is a figure explaining the difference of the signal distribution of the lung field area | region of the maximum expiration position and the maximum inspiration position. It is a figure which shows the example of a division | segmentation of an area | region. It is a figure which shows the example of a division | segmentation of an area | region. It is a figure which shows the signal value variation | change_quantity for every area | region. It is an example of a display of a dynamic picture and an image figure of presumed ventilation. It is a figure which shows the image figure in an expiration phase. It is a figure which shows the image figure in an intake phase.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Dynamic image processing system 10 Imaging device 11 X-ray source 12 Detector 13 Reading part 14 Cycle detection part 20 Imaging console 21 Control part 23 Operation part 30 Diagnosis console 31 Control part 34 Display part 40 Image processing apparatus 46 Image processing part 47 Image Analysis Unit 50 Server

Claims (4)

Imaging means for dynamically imaging the chest of a subject and generating dynamic images at a plurality of time phases for at least one respiratory phase;
Information on the absolute ventilation volume between the maximum expiratory position and the maximum inspiratory position in the respiratory phase is obtained, and a signal between the absolute expiratory volume and the dynamic image of the maximum expiratory position and the maximum inspiratory position among the generated dynamic images. An image analysis means for calculating an estimated ventilation volume per unit signal change amount from a change amount of the value, and calculating an estimated ventilation volume in each time phase using the estimated ventilation volume value per unit signal value;
Display means;
Control means for displaying the estimated ventilation volume calculated for each time phase on the display means;
A dynamic image processing system comprising:   The dynamic image processing system according to claim 1, wherein the control unit displays a numerical value indicating the calculated estimated ventilation amount.   3. The control unit according to claim 1, wherein the control unit generates an image image indicating the calculated estimated ventilation amount in a lung field region of each dynamic image, and continuously displays the image image according to a time phase. The dynamic image processing system described. The image analysis means divides a lung field region included in the dynamic image into a plurality of regions, calculates the estimated ventilation for each of the divided regions,
The dynamic image processing system according to claim 1, wherein the control unit displays an estimated ventilation amount calculated for each of the divided regions in the dynamic image.

Images