JP2019118710A - Medical image processing device, x-ray diagnostic device, and medical image processing program - Google Patents

Abstract

To improve visibility of X-ray image data including a device irrespective of the presence/absence of a marker.SOLUTION: A medical image processing device includes an acquisition unit, an extraction unit, a generation unit, and a correction unit. The acquisition unit acquires a plurality of X-ray images. The extraction unit extracts a region in which a tip region of a device is drawn in each of the plurality of the acquired X-ray images. The generation unit generates a plurality of feature points based on the extracted region. The correction unit performs correction of positions with respect to the plurality of X-ray images so that reference points based on the plurality of generated feature points become substantially the same position.SELECTED DRAWING: Figure 1

Description

  Embodiments of the present invention relate to a medical image processing apparatus, an X-ray diagnostic apparatus, and a medical image processing program.

  The position of a device such as a catheter, a guide wire, or a stent used in endovascular treatment may change due to a heartbeat or body movement of a subject. When multiple x-ray images are collected for such a device, the position at which the device is rendered varies for each x-ray image. Here, there is known a technique of detecting a marker attached to a device on an X-ray image and correcting the position of each X-ray image based on the detected marker. This makes it possible to display the device as if it stopped on the X-ray image, and to improve the visibility of the device.

JP, 2010-128578, A

  The problem to be solved by the present invention is to improve the visibility of X-ray image data including a device regardless of the presence or absence of a marker.

  The medical image processing apparatus according to the embodiment includes an acquisition unit, an extraction unit, a generation unit, and a correction unit. The acquisition unit acquires a plurality of X-ray images. The extraction unit extracts a region in which the tip region of the device is depicted in each of the plurality of acquired X-ray images. The generation unit generates a plurality of feature points based on the extracted area. The correction unit corrects the position of the plurality of X-ray images such that the reference points based on the plurality of generated feature points are at substantially the same position.

FIG. 1 is a block diagram showing an example of the configuration of a medical information processing system according to the first embodiment. FIG. 2 is a block diagram showing an example of the configuration of the X-ray diagnostic apparatus according to the first embodiment. FIG. 3 is a view showing an example of X-ray image data according to the first embodiment. FIG. 4 is a diagram for describing generation of feature points according to the first embodiment. FIG. 5 is a diagram for describing generation of feature points according to the first embodiment. FIG. 6 is a diagram for describing display of X-ray image data according to the first embodiment. FIG. 7 is a flowchart for explaining a series of processing of the medical image processing apparatus according to the first embodiment. FIG. 8 is a diagram for explaining generation of feature points according to the second embodiment. FIG. 9 is a view showing an example of a processing circuit in the X-ray diagnostic apparatus according to the second embodiment.

  Hereinafter, embodiments of a medical image processing apparatus, an X-ray diagnostic apparatus, and a medical image processing program will be described in detail with reference to the drawings.

First Embodiment
First, the first embodiment will be described. In the first embodiment, a medical information processing system including a medical image processing apparatus will be described as an example.

  As shown in FIG. 1, the medical information processing system 1 according to the first embodiment includes an X-ray diagnostic apparatus 10, an image storage apparatus 20, and a medical image processing apparatus 30. Here, FIG. 1 is a block diagram showing an example of the configuration of the medical information processing system 1 according to the first embodiment. As shown in FIG. 1, the X-ray diagnostic apparatus 10, the image storage apparatus 20, and the medical image processing apparatus 30 are mutually connected via a network.

  The X-ray diagnostic apparatus 10 acquires X-ray image data from the subject P. For example, the X-ray diagnostic apparatus 10 acquires a plurality of X-ray image data from the subject P, and transmits the acquired plurality of X-ray image data to the image storage apparatus 20 or the medical image processing apparatus 30. The configuration of the X-ray diagnostic apparatus 10 will be described later.

  The image storage device 20 stores a plurality of X-ray image data collected by the X-ray diagnostic device 10. For example, the image storage device 20 is realized by computer equipment such as a server device. In the present embodiment, the image storage apparatus 20 acquires a plurality of X-ray image data from the X-ray diagnostic apparatus 10 via the network, and the acquired plurality of X-ray image data is provided inside or outside the apparatus. Store in memory.

  The medical image processing apparatus 30 acquires a plurality of time-series X-ray image data via a network, and executes various processes using the acquired plurality of X-ray image data. For example, the medical image processing apparatus 30 is realized by computer equipment such as a workstation. In the present embodiment, the medical image processing apparatus 30 acquires a plurality of X-ray image data from the X-ray diagnostic apparatus 10 or the image storage apparatus 20 via a network. The medical image processing apparatus 30 also corrects the position of the plurality of acquired X-ray image data. The correction of the position of the plurality of X-ray image data will be described later.

  As shown in FIG. 1, the medical image processing apparatus 30 includes an input interface 31, a display 32, a memory 33, and a processing circuit 34.

  The input interface 31 includes a track ball for performing various instructions and various settings, switches, buttons, a mouse, a keyboard, a touch pad for performing an input operation by touching the operation surface, and a display screen and touch pad integrated with each other. It is realized by a touch screen, a non-contact input circuit using an optical sensor, an audio input circuit, and the like. The input interface 31 converts an input operation received from the operator into an electrical signal and outputs the signal to the processing circuit 34. The input interface 31 is not limited to one having physical operation parts such as a mouse and a keyboard. For example, an electrical signal processing circuit that receives an electrical signal corresponding to an input operation from an external input device provided separately from the medical image processing apparatus 30 and outputs the electrical signal to the processing circuit 34 is also included in the input interface 31. Included in the example.

  The display 32 displays various information. For example, the display 32 displays a graphical user interface (GUI) for receiving an instruction of the operator, and various X-ray image data. For example, the display 32 is a liquid crystal display or a CRT (Cathode Ray Tube) display.

  The memory 33 is realized by, for example, a random access memory (RAM), a semiconductor memory device such as a flash memory, a hard disk, an optical disk or the like. For example, the memory 33 stores a plurality of X-ray image data acquired from the image storage device 20. Further, for example, the memory 33 stores a program for each circuit included in the medical image processing apparatus 30 to realize its function.

  The processing circuit 34 controls the overall operation of the medical image processing apparatus 30 by executing the acquisition function 34 a, the extraction function 34 b, the generation function 34 c, the correction function 34 d, and the display control function 34 e.

  For example, the processing circuit 34 acquires a plurality of X-ray image data from the image storage device 20 by reading a program corresponding to the acquisition function 34 a from the memory 33 and executing the program. Also, for example, the processing circuit 34 reads out and executes a program corresponding to the extraction function 34 b from the memory 33 to draw out the tip region of the device in each of the plurality of X-ray image data acquired by the acquisition function 34 a. Extract the area that has been Further, for example, the processing circuit 34 generates a plurality of feature points based on the area extracted by the extraction function 34 b by reading out and executing a program corresponding to the generation function 34 c from the memory 33. Also, for example, the processing circuit 34 reads out and executes a program corresponding to the correction function 34 d from the memory 33 so that the reference points based on the plurality of feature points generated by the generation function 34 c become substantially the same position. Then, position correction is performed on a plurality of X-ray image data. Further, for example, the processing circuit 34 causes the display 32 to display the X-ray image data whose position has been corrected by the correction function 34 d by reading and executing a program corresponding to the display control function 34 e from the memory 33.

  In the medical image processing apparatus 30 shown in FIG. 1, each processing function is stored in the memory 33 in the form of a program executable by a computer. The processing circuit 34 is a processor that realizes a function corresponding to each program by reading and executing the program from the memory 33. In other words, the processing circuit 34 in the state where each program is read has a function corresponding to the read program. Although FIG. 1 is described as the acquisition function 34a, the extraction function 34b, the generation function 34c, the correction function 34d, and the display control function 34e in a single processing circuit 34, a plurality of independent processors are used. The processing circuit 34 may be configured in combination and each processor may execute a program to realize the function.

  Next, the X-ray diagnostic apparatus 10 for collecting a plurality of X-ray image data will be described with reference to FIG. FIG. 2 is a block diagram showing an example of the configuration of the X-ray diagnostic apparatus 10 according to the first embodiment. As shown in FIG. 2, the X-ray diagnostic apparatus 10 includes an X-ray high voltage apparatus 101, an X-ray tube 102, a collimator 103, a filter 104, a top plate 105, a C-arm 106, and an X-ray detector. A control unit 108, a memory 109, a display 110, an input interface 111, and a processing circuit 112 are provided.

  The X-ray high voltage apparatus 101 supplies a high voltage to the X-ray tube 102 under the control of the processing circuit 112. For example, the X-ray high voltage device 101 has an electrical circuit such as a transformer and a rectifier, and the high voltage generator generates a high voltage to be applied to the X-ray tube 102; And an X-ray controller for controlling an output voltage according to the X-ray. The high voltage generator may be a transformer type or an inverter type.

  The X-ray tube 102 is a vacuum tube having a cathode (filament) generating thermal electrons and an anode (target) generating an X-ray under collision of the thermal electrons. The X-ray tube 102 generates X-rays by irradiating thermal electrons from the cathode toward the anode using a high voltage supplied from the X-ray high voltage device 101.

  The collimator (also referred to as an X-ray diaphragm device) 103 has, for example, four slidable diaphragm blades. The collimator 103 causes the subject P to be irradiated with the X-rays generated by the X-ray tube 102 by sliding the diaphragm blade. Here, the diaphragm blade is a plate-like member made of lead or the like, and provided near the X-ray irradiation port of the X-ray tube 102 in order to adjust the irradiation range of the X-ray.

  The filter 104 changes the radiation quality of the X-ray to be transmitted depending on the material and thickness for the purpose of reducing the radiation dose to the subject P and improving the image quality of the X-ray image data. It reduces or reduces high energy components that cause a decrease in the contrast of X-ray image data. Further, the filter 104 changes the X-ray dose and the irradiation range depending on the material, thickness, position, etc., so that the X-ray irradiated from the X-ray tube 102 to the subject P has a predetermined distribution. Attenuates the line.

  The top 105 is a bed on which the subject P is placed, and is disposed on a bed (not shown). The subject P is not included in the X-ray diagnostic apparatus 10.

  The C-arm 106 holds the X-ray tube 102, the collimator 103 and the filter 104, and the X-ray detector 107 so as to face each other across the subject P. In addition, in FIG. 2, although the case where the X-ray diagnostic apparatus 10 is a single plane is mentioned as an example and demonstrated, an embodiment is not limited to this, The case of a biplane may be sufficient.

  The X-ray detector 107 is, for example, an X-ray flat panel detector (FPD) having detection elements arranged in a matrix. The X-ray detector 107 detects an X-ray irradiated from the X-ray tube 102 and transmitted through the subject P, and outputs a detection signal corresponding to the detected X-ray dose to the processing circuit 112. The X-ray detector 107 may be an indirect conversion detector having a grid, a scintillator array, and an optical sensor array, or may be a direct conversion detector having a semiconductor element for converting incident X-rays into electrical signals. It may be a detector.

  The controller 108 includes drive mechanisms such as a motor and an actuator, and a circuit that controls this mechanism. The control device 108 controls the operation of the collimator 103, the filter 104, the top plate 105, the C-arm 106 and the like under the control of the processing circuit 112. For example, the control device 108 controls the irradiation range of the X-ray irradiated to the subject P by adjusting the opening degree of the diaphragm blade of the collimator 103. Further, the control device 108 adjusts the position of the filter 104 to control the distribution of the dose of X-rays irradiated to the subject P. Also, for example, the control device 108 rotates and moves the C-arm 106 and moves the top 105.

  The memory 109 is realized by, for example, a RAM, a semiconductor memory element such as a flash memory, a hard disk, an optical disk or the like. The memory 109 receives and stores, for example, X-ray image data collected by the processing circuit 112. The memory 109 also stores programs corresponding to various functions read and executed by the processing circuit 112.

  The display 110 displays various information. For example, the display 110 displays a GUI for receiving an instruction of the operator and various X-ray image data. For example, the display 110 is a liquid crystal display or a CRT display.

  The input interface 111 includes a track ball for performing various instructions and various settings, switches, buttons, a mouse, a keyboard, a touch pad for performing an input operation by touching the operation surface, and a display screen and touch pad integrated with each other. It is realized by a touch screen, a non-contact input circuit using an optical sensor, an audio input circuit, and the like. The input interface 111 converts an input operation received from the operator into an electrical signal and outputs the signal to the processing circuit 112. The input interface 111 is not limited to one having physical operation parts such as a mouse and a keyboard. For example, an electrical signal processing circuit that receives an electrical signal corresponding to an input operation from an external input device provided separately from the X-ray diagnostic apparatus 10 and outputs the electrical signal to the processing circuit 112 is also included in the input interface 111. Included in the example.

  The processing circuit 112 controls the overall operation of the X-ray diagnostic apparatus 10 by executing the control function 112a, the acquisition function 112b, and the display control function 112c. For example, the processing circuit 112 controls various functions of the processing circuit 112 based on an input operation received from the operator via the input interface 111 by reading and executing a program corresponding to the control function 112 a from the memory 109. Do.

  Further, the processing circuit 112 acquires X-ray image data by reading and executing a program corresponding to the acquisition function 112 b from the memory 109. For example, the collection function 112 b controls the X-ray high voltage apparatus 101 and adjusts the voltage supplied to the X-ray tube 102 to control the X dose and the on / off of the object P to be irradiated. Further, the collection function 112 b controls the control device 108 to adjust the opening degree of the diaphragm blade of the collimator 103 to control the irradiation range of the X-ray irradiated to the subject P. The collection function 112 b also controls the controller 108 to adjust the position of the filter 104 to control the distribution of the X-ray dose. Further, the collection function 112 b controls the control device 108 to control rotation and movement of the C-arm 106, movement of the top 105, and the like. Further, the acquisition function 112 b generates X-ray image data based on the detection signal received from the X-ray detector 107, and stores the generated X-ray image data in the memory 109. Here, the collecting function 112 b may be configured to perform various types of image processing on the X-ray image data stored in the memory 109. For example, the acquisition function 112 b performs noise reduction processing using an image processing filter and scattered radiation correction on X-ray image data.

  Further, the processing circuit 112 reads out and executes a program corresponding to the display control function 112 c from the memory 109 to display the X-ray image data acquired by the acquisition function 112 b on the display 110. Further, the display control function 112 c causes the display 110 to display a GUI for receiving an instruction of the operator.

  In the X-ray diagnostic apparatus 10 shown in FIG. 2, each processing function is stored in the memory 109 in the form of a computer-executable program. The processing circuit 112 is a processor that realizes a function corresponding to each program by reading and executing the program from the memory 109. In other words, the processing circuit 112 in the state of reading each program has a function corresponding to the read program. Although FIG. 2 is described as that the control function 112a, the collecting function 112b, and the display control function 112c are realized by a single processing circuit 112, the processing circuit 112 is configured by combining a plurality of independent processors. The functions may be realized by the processors executing programs.

  The word “processor” used in the above description is, for example, a central processing unit (CPU), a graphics processing unit (GPU), an application specific integrated circuit (ASIC), a programmable logic medical device (for example, This means circuits such as Simple Programmable Logic Device (SPLD), Complex Programmable Logic Device (CPLD), and Field Programmable Gate Array (FPGA). The processor implements a function by reading and executing a program stored in the memory 33 or the memory 109. Instead of storing the program in the memory 33 or the memory 109, the program may be directly incorporated in the circuit of the processor. In this case, the processor implements the function by reading and executing a program embedded in the circuit. Note that the processor according to the present embodiment is not limited to the case where each processor is configured as a single circuit, and a plurality of independent circuits may be combined to be configured as a single processor to realize its function. .

  The medical information processing system 1 including the medical image processing apparatus 30 has been described above. Under such a configuration, the medical image processing apparatus 30 in the medical information processing system 1 performs the processing by the processing circuit 34, which will be described in detail below, to recognize the visibility of the X-ray image data including the device regardless of the presence or absence of the marker. Improve. The processing performed by the medical image processing apparatus 30 according to the first embodiment will be described in detail below.

  First, the acquisition function 112 b of the X-ray diagnostic apparatus 10 acquires a plurality of X-ray image data. For example, the collection function 112b continuously or intermittently irradiates the heart of the subject P in which the device is inserted into the coronary artery, continuously or intermittently during a period according to an instruction from the operator. At this time, the X-ray detector 107 detects X-rays transmitted through the heart of the subject P, and outputs a detection signal corresponding to the detected X-ray dose to the processing circuit 112.

  Then, based on the detection signal received from the X-ray detector 107, the acquisition function 112b generates, in time series, a plurality of X-ray image data in which devices in the blood vessel of the subject P are visualized. For example, the acquisition function 112b generates a plurality of X-ray image data including the X-ray image data I11 shown in FIG. FIG. 3 is a view showing an example of X-ray image data according to the first embodiment.

  In FIG. 3, a guide wire D1 having a tip region is shown as an example of a device inserted into a subject P. Here, the distal end region is a portion located at the distal end of the guide wire D1 and depicted in the X-ray image data more deeply than the other portions of the guide wire D1. For example, the tip region is made to have a large mass per unit length. As a result, the X-rays transmitted through the distal end region are significantly attenuated compared to the X-rays transmitted through the other region of the guide wire D1 and the X-rays transmitted through the region other than the guide wire D1. It is depicted darkly.

  For example, the distal end region is a large diameter portion of the guide wire D1. Also, for example, the tip region is a portion made of a material having a higher density than the other portions in the guide wire D1. Also, for example, the tip end region is a portion where the number of turns (the number of turns per unit length) of the coil constituting the outer surface of the guide wire D1 is large. Not only the guide wire D1 but also the device inserted into the blood vessel has a great need to grasp the position of the tip, so in many cases, it has a tip region drawn darkly in the X-ray image data.

  After acquiring a plurality of X-ray image data including the X-ray image data I11, the X-ray diagnostic apparatus 10 transmits the acquired plurality of X-ray image data to the image storage device 20. Further, the image storage device 20 stores the plurality of X-ray image data transmitted from the X-ray diagnostic device 10 in a memory provided inside or outside the device. Next, the acquisition function 34 a of the medical image processing apparatus 30 acquires a plurality of X-ray image data from the image storage apparatus 20. The acquisition function 34 a may be a case where a plurality of X-ray image data is acquired from the X-ray diagnostic apparatus 10 without the image storage device 20. Then, the acquisition function 34 a stores the acquired plurality of X-ray image data in the memory 33.

  Next, the extraction function 34b reads a plurality of X-ray image data from the memory 33, and extracts a region in which the tip region is depicted in each of the plurality of read X-ray image data. Next, the generation function 34 c generates a plurality of feature points based on the extracted area. Hereinafter, this point will be described with reference to FIG. FIG. 4 is a diagram for describing generation of feature points according to the first embodiment.

  For example, as illustrated in FIG. 4, the extraction function 34 b extracts, in the X-ray image data I11, a region R11 in which the tip region of the guide wire D1 is drawn. As an example, the extraction function 34b performs high-frequency image conversion on the X-ray image data I11 to extract the region R11. Hereinafter, the X-ray image data I11 from which the region R11 is extracted will be referred to as X-ray image data I12.

  Next, the generation function 34c extends or shortens the region R11 in the length direction. For example, the generation function 34c deforms the region R11 so as to extend or shorten the region R11 in the length direction by the morphological operation on the X-ray image data I12. Hereinafter, X-ray image data I12 in which the region R11 is extended or shortened in the length direction will be referred to as X-ray image data I13. Moreover, below, the area | region R11 extended or shortened in the length direction is described as process area | region R12.

  The method of extending or shortening the region R11 in the longitudinal direction is not limited to the morphological operation, and any method of substantially changing the length of the region R11 can be used. For example, the generation function 34c deletes the predetermined number of pixels in the longitudinal direction among the pixels at the end of the region R11 (such as the number of pixels approximately the same as the number of pixels in the radial direction of the tip region). Shorten the length direction. Also, for example, the generation function 34c extends the region R11 in the length direction by adding a predetermined number of pixels to the end of the region R11. In addition, for example, the generation function 34c may set the pixel value of a predetermined number of pixels in the longitudinal direction among the pixels at the end in the longitudinal direction of the region R11 to the same value as the pixel value in the pixels in the region By replacing with the pixel value, the region R11 is shortened in the length direction. In addition, for example, the generation function 34c replaces the pixel values of a predetermined number of pixels adjacent to the end in the lengthwise direction of the region R11 with pixel values similar to the pixel values in the pixels in the region R11. The region R11 is extended in the longitudinal direction. In the following, the case where the region R11 is shortened in the length direction will be described as an example.

  Next, the generation function 34c generates a plurality of feature points by performing differential processing between a region R11 in which the distal end region of the guide wire D1 is drawn and a processing region R12 in which the region R11 is shortened in the length direction. . For example, as illustrated in FIG. 4, the generation function 34 c subtracts the pixel value of the corresponding pixel between the X-ray image data I12 and the X-ray image data I13 to obtain a difference between the region R11 and the processing region R12. Do the processing. Thereby, the area | region corresponding to process area | region R12 is differed among area | region R11, and the both ends of area | region R11 are produced | generated as two feature points. Image data obtained by subtracting the pixel values of corresponding pixels of the X-ray image data I12 and the X-ray image data I13 is referred to as difference image data I14.

  Here, the generation function 34c may be a case where the feature point is generated by processing a difference area obtained by subtracting the area R11 and the processing area R12. For example, when difference processing between the region R11 and the processing region R12 is simply performed, the difference region has a shape corresponding to the shapes of both ends of the region R11 and the processing region R12. On the other hand, the generation function 34 c can generate feature points by, for example, deforming the difference area so as to be circular.

  Next, another example of the generation of feature points by the generation function 34 c will be described using FIG. 5. FIG. 5 is a diagram for describing generation of feature points according to the first embodiment. First, in the X-ray image data I11, the extraction function 34b extracts a region R11 in which the tip region of the guide wire D1 is drawn.

  Next, the generation function 34 c generates X-ray image data I 13 including the processing area R 12 by extending or shortening the extracted area R 11 in the length direction. The generation function 34c also generates X-ray image data I15 including the processing area R13 by extending or shortening the extracted area R11 in the length direction. Here, the generation function 34c extends or shortens the processing area R12 and the processing area R13 so that the lengths of the processing area R12 and the processing area R13 are different. For example, as illustrated in FIG. 5, the generation function 34 c sets a region R11 shortened in the length direction as a processing region R12, and sets a region R11 extended in the length direction as a processing region R13.

  Then, the generation function 34c generates a plurality of feature points by performing differential processing between the processing area R12 and the processing area R13. For example, as shown in FIG. 5, the generation function 34c subtracts the pixel value of the corresponding pixel between the X-ray image data I13 and the X-ray image data I15 to obtain the processing area R12 and the processing area R13. Perform differential processing. As a result, the area corresponding to the processing area R12 in the processing area R13 is differentiated, and both ends of the processing area R13 are generated as two feature points. Image data obtained by subtracting the pixel values of corresponding pixels of the X-ray image data I13 and the X-ray image data I15 is referred to as difference image data I16.

  As described with reference to FIGS. 4 and 5, the extraction function 34b extracts the region R11 in which the tip region of the guide wire D1 is drawn in the X-ray image data I11, and the generation function 34c is based on the region R11. To generate a plurality of feature points. Similarly, the extraction function 34b extracts an area in which the distal end area of the guide wire D1 is depicted in each of the plurality of X-ray image data, and the generation function 34c generates a plurality of feature points based on the extracted area. Generate

  Next, the correction function 34d corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position.

  For example, the correction function 34d sets two feature points generated for each of a plurality of X-ray image data as a reference point, and the plurality of set reference points have substantially the same position. Position correction is performed on the X-ray image data. As an example, the correction function 34d performs pattern matching using a shape template to extract two feature points in each X-ray image data, and a plurality of X-ray images using the extracted two feature points as reference points. Perform position correction on data. In this case, the position and angle of the distal end region of the guide wire D1 are substantially fixed among the plurality of X-ray image data.

  In pattern matching, when the target to be extracted is circular, computational resources and time are reduced as compared with the case where the target to be extracted is not circular. This is because when extracting an object such as a rectangle by pattern matching, it is necessary to perform pattern matching in each direction while rotating a shape template corresponding to the shape of the object, while extracting a circular object This is because it is sufficient to perform pattern matching in one direction using a circular template. Therefore, the correction function 34d can easily extract the feature points in the X-ray image data by the generation function 34c generating the feature points in a circular shape.

  Also, for example, the correction function 34d sets any one of two feature points generated for each of the plurality of X-ray image data as a reference point. As an example, the correction function 34d sets a feature point on the tip end side of the guide wire D1 of the two feature points as a reference point, and sets a plurality of X-rays so that the set reference points become substantially the same position. Position correction is performed on image data. In this case, the tip position of the guide wire D1 is substantially fixed among the plurality of X-ray image data, and the angle of the tip region changes for each X-ray image data.

  Here, the correction function 34d performs a plurality of corrections to the plurality of X-ray image data such that one reference point set for each X-ray image data is substantially the same position. The correction of the angle may be performed on the X-ray image data. For example, the correction function 34d calculates angles relating to a plurality of feature points for each of a plurality of X-ray image data, and corrects the angles with respect to a plurality of X-ray image data so that the calculated angles become substantially the same. Do.

  As an example, the correction function 34d first determines, in each of the plurality of X-ray image data, an angle between a line connecting two feature points and a reference line in the X-ray image data as an angle with respect to the plurality of feature points. calculate. Then, the correction function 34d performs correction processing such as rotational movement on a part or all of the plurality of X-ray image data so that the calculated angle is substantially the same among the plurality of X-ray image data. In this case, the position and angle of the distal end region of the guide wire D1 are substantially fixed among the plurality of X-ray image data.

  In addition, although the case where the feature point is set as the reference point has been described, the reference point is not limited to the feature point. For example, the correction function 34d sets a point based on the positional relationship of the plurality of feature points as a reference point for each of the plurality of X-ray image data. Here, the point based on the positional relationship between the plurality of feature points is, for example, a middle point of two feature points in each X-ray image data, another internally split point, an externally split point, or the like.

  As an example, the correction function 34d sets the middle point of the two feature points generated for each of the plurality of X-ray image data as a reference point so that the set reference points become substantially the same position, Position correction is performed on a plurality of X-ray image data. Here, the correction function 34d may further perform angle correction on a plurality of X-ray image data.

  In addition, as an example, the correction function 34d is a middle point of two feature points generated for each of a plurality of X-ray image data and one of two feature points (for example, a feature on the tip side of the guide wire D1 The points are set as reference points, and position correction is performed on a plurality of X-ray image data so that the set reference points become substantially the same position. As an example, the correction function 34d internally divides the line connecting two feature points generated for each of the plurality of X-ray image data into 1: 2 and 2: 1. A point is set as a reference point, and position correction is performed on a plurality of X-ray image data so that the set reference points become substantially the same position.

  The correction function 34d may set three or more reference points. For example, the correction function 34d sets two feature points generated for each of the plurality of X-ray image data and the middle point of the two feature points as reference points, and the set reference points are substantially the same position As a result, position correction is performed on a plurality of X-ray image data. Here, when the position correction is performed on a plurality of X-ray image data so that the set three reference points become substantially the same position, the tip of the guide wire D1 is among the plurality of X-ray image data. The position and angle of the area are substantially fixed.

  Then, the display control function 34 e causes the display 32 to display the X-ray image data whose position has been corrected by the correction function 34 d. Here, the display control function 34 e may use the entire X-ray image data as a display area or a part as a display area. Hereinafter, a case where a part of X-ray image data is displayed as a display area will be described with reference to FIG. FIG. 6 is a diagram for describing display of X-ray image data according to the first embodiment. FIG. 6 shows a case where a part of the position-corrected X-ray image data I11 is displayed on the display 32 as a display area.

  In the display area A1 shown in FIG. 6, the display control function 34e is the other end (hereinafter referred to as end E1) of the ends in the longitudinal direction of the distal end area of the guide wire D1 corresponding to the distal end of the guide wire D1. Hereinafter, a case where the X-ray image data I11 is displayed on the display 32 such that the end E2) is located away from the center C1 of the display area A1 will be described. For example, in the display control function 34e, the display area A1 is positioned such that the end E1 is at a predetermined position near the center C1 or the center C1, and the end E2 is located on a half straight line connecting the center C1 and the end E1 starting from the center C1. The display area A1 in the X-ray image data I11 is displayed on the display 32 after setting.

  When the display is made in this manner, a region beyond the tip of the guide wire D1 is displayed widely in the display region A1. Here, when a procedure for advancing the guide wire D1 is performed in the blood vessel, the operator who operates the guide wire D1 is an area where the guide wire D1 advances from now (an area ahead of the tip of the guide wire D1) I am often interested in Therefore, the display control function 34e can facilitate the operation of advancing the guide wire D1 in the blood vessel by displaying the display area A1.

  The display area A2 shown in FIG. 6 causes the display control function 34e to display the X-ray image data I11 on the display 32 such that the middle point of the distal end area of the guide wire D1 is located at the center C2 of the display area A2. Indicates the case. For example, the display control function 34e sets the display area A2 so that the midpoint of the line connecting the end E1 and the end E2 is located at the center C2, and displays the display area A2 in the X-ray image data I11 on the display 32. Let When such display is performed, the distal end region of the guide wire D1 is displayed at the center, and observation of the distal end region can be facilitated.

  Although the case of displaying the X-ray image data whose position has been corrected by the correction function 34d has been described above, the embodiment is not limited to this. For example, the display control function 34e may be a case where the display 32 displays X-ray image data that is X-ray image data whose position has been corrected by the correction function 34d, and on which image processing has been further performed.

  For example, first, the correction function 34d adds the pixel values of corresponding pixels among the plurality of position-corrected X-ray image data. As an example, the correction function 34d may apply a predetermined weighting to the pixel values of the pixels constituting the X-ray image data to be processed among the plurality of X-ray image data collected in time series. The pixel values of the pixels constituting the line image data are added. Thus, high frequency noise is reduced in the X-ray image data to be processed. Then, the display control function 34 e causes the display 32 to display the X-ray image data added by the correction function 34 d. Here, the display control function 34 e may set the whole of the X-ray image data subjected to the addition processing as a display area, or may set a part as a display area.

  Also, the case of performing post-processing has been described as an example. That is, in the embodiment described above, the acquisition function 34 a stores the plurality of X-ray image data acquired from the image storage device 20 or the X-ray diagnostic apparatus 10 in the memory 33, and the extraction function 34 b reads the plurality of X-ray image data from the memory 33. In each of the X-ray image data, a region where the tip region is drawn is extracted, the generation function 34 c generates a plurality of feature points based on the extracted region, and the correction function 34 d generates a plurality of The case where position correction is performed on a plurality of X-ray image data has been described so that reference points based on the feature points are substantially at the same position. However, the embodiment is not limited to this.

  For example, the correction function 34d may perform position correction in real time as the X-ray diagnostic apparatus 10 acquires X-ray image data. In this case, first, the acquisition function 34 a sequentially acquires the X-ray image data acquired by the X-ray diagnostic apparatus 10. Further, the extraction function 34 b sequentially extracts the region in which the tip region is drawn in each of the plurality of acquired X-ray image data, and the generation function 34 c extracts the plurality of feature points based on the extracted region. Generate sequentially. Then, the correction function 34d sequentially corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position. At this time, the display control function 34 e causes the display image on the display 32 to be displayed while being updated with the position-corrected X-ray image data each time the position correction is performed by the correction function 34 d.

  Next, an example of a procedure of processing by the X-ray diagnostic apparatus 10 will be described using FIG. FIG. 7 is a flowchart for describing a series of processing of the medical image processing apparatus 30 according to the first embodiment. Steps S101 and S107 are steps corresponding to the acquisition function 34a. Step S102 corresponds to the extraction function 34b. Step S103 is a step corresponding to the generation function 34c. Steps S104 and S105 correspond to the correction function 34d. Step S106 is a step corresponding to the display control function 34e.

  First, the processing circuit 34 acquires a plurality of X-ray image data from the image storage device 20 or the X-ray diagnostic device 10 (step S101). Next, the processing circuit 34 extracts a region R11 in which the tip region of the guide wire D1 is depicted in each of the plurality of acquired X-ray image data (step S102). Next, the processing circuit 34 generates a plurality of feature points based on the extracted region R11 (step S103).

  Next, the processing circuit 34 corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position (step S104). The processing circuit 34 adds the pixel values of the corresponding pixels among the plurality of X-ray image data whose position has been corrected (step S105). Then, the processing circuit 34 causes the display 32 to display the X-ray image data subjected to the addition processing (step S106).

  Here, the processing circuit 34 further determines whether X-ray image data has been acquired (step S107). Furthermore, when the X-ray image data is acquired (Yes at Step S107), the processing circuit 34 proceeds to Step S102 again. On the other hand, when the X-ray image data is not acquired (No at Step S107), the processing circuit 34 ends the processing.

  Step S105 may not be performed. In this case, the processing circuit 34 causes the display 32 to display the position-corrected X-ray image data in step S106.

  As described above, according to the first embodiment, the acquisition function 34a acquires a plurality of X-ray image data. The extraction function 34 b extracts a region R <b> 11 in which the tip region of the guide wire D <b> 1 is depicted in each of the plurality of acquired X-ray image data. The generation function 34c generates a plurality of feature points based on the extracted region R11. The correction function 34d corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position. Therefore, the medical image processing apparatus 30 according to the first embodiment can improve the visibility of the guidewire D1 to which the marker is not attached.

  Moreover, the medical image processing apparatus 30 can make unnecessary X-ray opaque metal etc. attached as a marker to a guide wire by improving visibility regardless of the presence or absence of a marker. Thus, the medical image processing apparatus 30 can release the restriction on the bending of the guide wire caused due to the marker, and can improve the operability of the guide wire.

  Further, according to the first embodiment, the correction function 34d adds the pixel values of corresponding pixels among the plurality of position-corrected X-ray image data. Further, the display control function 34 e causes the display 32 to display the X-ray image data subjected to the addition processing. Therefore, the medical image processing apparatus 30 according to the first embodiment can enhance the visibility after further emphasizing and displaying the guide wire D1 depicted in the X-ray image data.

  Further, according to the first embodiment, the display control function 34e displays the other end E2 of the ends in the longitudinal direction of the distal end region of the guide wire D1 corresponding to the end E1 corresponding to the distal end of the guide wire D1. The X-ray image data I11 is displayed on the display 32 so as to be located away from the center C1 of the area A1. That is, the display control function 34e displays a wide area in front of the tip of the guide wire D1. Therefore, the medical image processing apparatus 30 according to the first embodiment can present the region where the guidewire D1 advances from now to the operator with priority, and facilitate the operation of advancing the guidewire D1 in the blood vessel. it can.

  Further, according to the first embodiment, the correction function 34d corrects the position in real time as the X-ray diagnostic apparatus 10 collects X-ray image data. Therefore, the medical image processing apparatus 30 according to the first embodiment can facilitate the operation of the guide wire D1 in the blood vessel.

  For example, in a procedure for chronic total occlusion (CTO), a plaque that occludes a coronary artery is penetrated by a device such as a guide wire. In performing such an operation, the operator first advances the tip of the device to the vicinity of the plaque, and determines the position of the plaque into which the tip of the device is inserted. At this time, the X-ray diagnostic apparatus 10 sequentially acquires X-ray image data of the heart, and the correction function 34d corrects the position in real time as the X-ray diagnostic apparatus 10 acquires X-ray image data. Do. The display control function 34e causes the display image on the display 32 to be displayed while being updated with the position-corrected X-ray image data each time the position correction is performed by the correction function 34d. This allows the operator to determine the position to insert the tip of the device with reference to the current positional relationship between the plaque and the device.

  As an example, the correction function 34d sets one reference point based on a plurality of feature points, and corrects the position of a plurality of X-ray image data so that the set reference points become substantially the same position. Do. In this case, while securing the visibility by substantially fixing the position of the device of each X-ray image data, the angle of the device is updated in real time according to the operator operating the device. The operator can then insert the tip of the device into the plaque at any angle, referring to the current angle of the device. Similarly, after inserting the tip into the plaque, the operator can advance the device at any angle with reference to the current angle of the device to penetrate the plaque.

Second Embodiment
In the first embodiment described above, the case of generating a plurality of feature points based on the area R11 in which the tip area of one device (guide wire D1) is drawn has been described. On the other hand, in the second embodiment, a plurality of regions corresponding to tip regions of a plurality of devices are extracted, and a plurality of feature points are generated by generating feature points based on different regions. Will be explained.

  The medical image processing apparatus 30 according to the second embodiment has the same configuration as the medical image processing apparatus 30 shown in FIG. 1, and part of the processing by the extraction function 34 b and the generation function 34 c is different. Therefore, components having the same configuration as the configuration described in the first embodiment are assigned the same reference numerals as those in FIG. 1 and descriptions thereof will be omitted.

  First, the acquisition function 34a acquires a plurality of X-ray image data. For example, the acquisition function 34a acquires a plurality of X-ray image data including the X-ray image data I21 shown in FIG. FIG. 8 is a diagram for explaining generation of feature points according to the second embodiment.

  In FIG. 8, a guide wire D2 and a guide wire D3 are shown as an example of the device inserted into the subject P. For example, the guide wire D2 and the guide wire D3 are two devices inserted in the opposite direction to the same coronary artery in the subject P. For example, in the procedure for CTO, the guide wire D2 and the guide wire D3 are devices inserted along the blood flow direction toward the plaque that occludes the coronary artery, and along the reverse direction of the blood flow It is an inserted device. The guide wire D2 and the guide wire D3 each have a tip region as shown in FIG.

  Next, the extraction function 34 b extracts a plurality of areas respectively corresponding to the tip areas of the plurality of devices in each of the plurality of X-ray image data acquired by the acquisition function 34 a. For example, the extraction function 34b extracts, in the X-ray image data I21, a region R21 in which the tip region of the guide wire D2 is depicted and a region R31 in which the tip region of the guide wire D3 is depicted. Hereinafter, the X-ray image data I21 obtained by extracting the region R21 and the region R31 will be referred to as X-ray image data I22.

  Next, the generation function 34c extends or shortens the region R21 and the region R31 in the length direction, respectively. For example, the generation function 34c extends or shortens the area R21 and the area R31 in the length direction by the morphological operation on the X-ray image data I22. Hereinafter, X-ray image data I22 in which the region R21 and the region R31 are extended or shortened in the length direction will be referred to as X-ray image data I23. Moreover, below, the area | region R21 extended or shortened in the length direction is described as process area | region R22, and the area | region R31 extended or shortened in the length direction is described as process area | region R32. Moreover, below, the case where area | region R21 and area | region R31 are shortened to a length direction is demonstrated as an example.

  Next, the generation function 34c generates a plurality of feature points based on different regions by performing difference processing between the regions R21 and R31, and the processing region R22 and the processing region R32. For example, as shown in FIG. 8, the generation function 34c subtracts the pixel value of the corresponding pixel between the X-ray image data I22 and the X-ray image data I23 to generate the area R21 and the area R31, and the processing area A difference process with R22 and the processing area R32 is performed. Thereby, the area corresponding to the processing area R22 in the area R21 is differentiated, and one feature point corresponding to one end of the area R21 is generated. In addition, the region corresponding to the processing region R32 in the region R31 is differentiated, and one feature point corresponding to one end of the region R31 is generated. That is, the generation function 34c generates two feature points based on different regions by the difference processing shown in FIG. The image data obtained by subtracting the pixel values of the corresponding pixels of the X-ray image data I22 and the X-ray image data I23 will be referred to as difference image data I24.

  Here, FIG. 8 shows a case where one feature point based on the region R21 and one feature point based on the region R31 are generated. Specifically, FIG. 8 shows a case where the generation function 34c shortens each of the region R21 and the region R31 in the length direction with the position of one end fixed. Thus, when performing differential processing between the region R21 and the region R31 and the processing region R22 and the processing region R32, the end on the side where the position is fixed is differentiated, and the feature point corresponding to the other end is the region R21 and the region R31. Are generated one by one.

  The generation function 34c may be a case where both or one of the region R21 and the region R31 is shortened from both ends. For example, the generation function 34c generates the processing area R22 and the processing area R32 by shortening the area R21 and the area R31 from both ends. In this case, the generation function 34c generates two feature points based on the region R21 and two feature points based on the region R31 by subtracting the region R21 and the region R31, and the processing region R22 and the processing region R32.

  Next, the correction function 34d corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position. For example, the correction function 34d sets a feature point based on the region R21 and a feature point based on the region R31 as reference points, and sets a plurality of X-rays so that each of the set two reference points becomes substantially the same position. Position correction is performed on image data. Further, for example, the correction function 34d sets one reference point based on a plurality of feature points, and corrects the position of a plurality of X-ray image data so that the set reference points become substantially the same position. Do. Furthermore, the correction function 34d performs correction on the plurality of X-ray image data whose position has been corrected such that an angle relating to the feature point based on the region R21 and the feature point based on the region R31 is substantially the same among the plurality Correct the angle with respect to it. Thereby, the position and angle of the region between the guidewire D2 and the guidewire D3 are substantially fixed among the plurality of X-ray image data. Then, the display control function 34 e causes the display 32 to display the position-corrected X-ray image data.

As described above, the extraction function 34b according to the second embodiment extracts a plurality of regions respectively corresponding to the tip regions of the plurality of devices in each of the plurality of X-ray image data.
In addition, the generation function 34c generates a plurality of feature points by generating feature points based on different regions. Further, the correction function 34d corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of generated feature points become substantially the same position. Therefore, the medical image processing apparatus 30 according to the second embodiment can improve the visibility of the region between the plurality of devices regardless of the presence or absence of the marker.

  For example, in the medical image processing apparatus 30 according to the second embodiment, in the procedure for CTO, the position and angle of the region between the guide wire D2 and the guide wire D3 located on both sides of the plaque that occludes the coronary artery Display substantially fixed X-ray image data. In addition, for example, the medical image processing apparatus 30 displays the X-ray image data in which the position correction is performed in real time while at least one of the guide wire D2 and the guide wire D3 is operated. Present the current relative position of D2, guidewire D3 and plaque. Thereby, the medical image processing apparatus 30 can improve the visibility of the plaque and facilitate the procedure of penetrating the plaque. Similarly, in the X-ray image data, the medical image processing apparatus 30 can improve the visibility of an arbitrary area sandwiched by a plurality of devices.

  In the embodiment described above, a plurality of X-ray image data collected for the heart (coronary artery) of the subject P has been described. However, the medical image processing apparatus 30 can improve the visibility by correcting the position of the X-ray image data collected not only for the X-ray image data collected for the heart, but for any part. .

  Further, in the above-described embodiment, the X-ray image data in which a device having no marker is depicted has been described, but the embodiment is not limited thereto. For example, the medical image processing apparatus 30 extracts two markers as feature points from X-ray image data in which a device having two markers is depicted, and performs position correction on the X-ray image data. Good. Also, for example, the medical image processing apparatus 30 extracts the feature points based on the marker and the feature points based on the area where the tip region of the device is drawn from the X-ray image data in which the device having one marker is drawn The position correction may be performed on the X-ray image data.

  In the embodiment described above, the case has been described where the medical image processing apparatus 30 includes the processing circuit 34 having the extraction function 34 b, the generation function 34 c, and the correction function 34 d. However, the embodiment is not limited to this. For example, the processing circuit 112 in the X-ray diagnostic apparatus 10 may have functions corresponding to the extraction function 34 b, the generation function 34 c, and the correction function 34 d. For example, as shown in FIG. 9, the processing circuit 112 has an extraction function 112d corresponding to the extraction function 34b, a generation function 112e corresponding to the generation function 34c, and a correction function 112f corresponding to the correction function 34d. FIG. 9 is a view showing an example of the processing circuit 112 in the X-ray diagnostic apparatus 10 according to the second embodiment.

  In this case, first, the acquisition function 112 b acquires a plurality of X-ray image data. Next, the extraction function 112 d extracts an area in which the tip area of the device is depicted in each of the plurality of X-ray image data acquired by the acquisition function 112 b. Next, the generation function 112e generates a plurality of feature points based on the area extracted by the extraction function 112d. Next, the correction function 112 f corrects the position of the plurality of X-ray image data so that the reference points based on the plurality of feature points generated by the generation function 112 e become substantially the same position. Then, the display control function 112 c causes the display 110 to display the X-ray image data whose position has been corrected by the correction function 112 f.

  Each component of each device according to the embodiment described above is functionally conceptual, and does not necessarily have to be physically configured as illustrated. That is, the specific form of the dispersion and integration of each device is not limited to the illustrated one, and all or a part thereof is functionally or physically dispersed in any unit depending on various loads, usage conditions, etc. It can be integrated and configured. Furthermore, all or any part of each processing function performed in each device may be realized by a CPU and a program analyzed and executed by the CPU, or may be realized as wired logic hardware.

  Further, the medical image processing method described in the above-described embodiment can be realized by executing a prepared medical image processing program on a computer such as a personal computer or a workstation. The medical image processing program can be distributed via a network such as the Internet. Moreover, this medical image processing program is recorded on a non-transitory recording medium readable by a computer such as a hard disk, flexible disk (FD), CD-ROM, MO, DVD, etc., and read from the recording medium by the computer. It can also be performed by

  According to at least one embodiment described above, the visibility of the X-ray image data including the device can be improved regardless of the presence or absence of the marker.

  While certain embodiments of the present invention have been described, these embodiments have been presented by way of example only, and are not intended to limit the scope of the invention. These embodiments can be implemented in other various forms, and various omissions, replacements and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the invention described in the claims and the equivalents thereof as well as included in the scope and the gist of the invention.

10 X-ray diagnostic apparatus 30 medical image processing apparatus 34 processing circuit 34a acquisition function 34b extraction function 34c generation function 34d correction function 34e display control function

Claims (20)

An acquisition unit for acquiring a plurality of X-ray images;
An extraction unit for extracting an area in which the tip area of the device is depicted in each of the plurality of acquired X-ray images;
A generation unit that generates a plurality of feature points based on the extracted area;
A correction unit that performs position correction on the plurality of X-ray images such that the reference points based on the plurality of generated feature points become substantially the same position;
A medical image processing apparatus comprising:   The medical image processing apparatus according to claim 1, wherein the generation unit generates the plurality of feature points by performing differential processing between the area and a processing area in which the area is extended or shortened in the length direction. .   The generation unit is configured such that a first processing area obtained by extending or shortening the area in the length direction and a second processing area obtained by extending or reducing the area in the length direction so that the length is different from the first processing area. The medical image processing apparatus according to claim 1, wherein the plurality of feature points are generated by performing differential processing with a processing region.   The medical image processing apparatus according to any one of claims 1 to 3, further comprising a display control unit that causes the display unit to display an X-ray image whose position has been corrected by the correction unit. The correction unit adds the pixel values of corresponding pixels among the plurality of X-ray images whose positions are corrected,
The medical image processing apparatus according to claim 4, wherein the display control unit causes the display unit to display the X-ray image added by the correction unit.   The display control unit is configured such that the other end of the longitudinal end of the tip region of the device is located farther from the center of the display area of the display unit than the end corresponding to the tip of the device. The medical image processing apparatus according to claim 4, wherein a line image is displayed on the display unit.   The medical image processing apparatus according to any one of claims 1 to 6, wherein the plurality of feature points are generated based on the area in which a tip area of one device is drawn. The extraction unit extracts, in each of the plurality of X-ray images, a plurality of the regions respectively corresponding to tip regions of the plurality of devices,
The medical image processing apparatus according to any one of claims 1 to 6, wherein the generation unit generates the plurality of feature points by respectively generating feature points based on different areas.   The correction unit sets at least two of the reference points based on the plurality of feature points, and corrects the position of the plurality of X-ray images such that each of the reference points is at substantially the same position. The medical image processing apparatus according to any one of claims 1 to 8, which is performed.   The medical image processing apparatus according to claim 9, wherein the correction unit sets at least two of the plurality of feature points as the reference point.   The medical image according to claim 9, wherein the correction unit sets, as the reference point, at least one feature point among the plurality of feature points and at least one point based on a positional relationship between the plurality of feature points. Processing unit.   The correction unit sets one of the reference points based on the plurality of feature points, and performs position correction on the plurality of X-ray images such that the reference points are at substantially the same position. Item 9. The medical image processing device according to any one of items 1 to 8.   The correction unit further calculates angles relating to the plurality of feature points for each of the plurality of X-ray images, and performs angle correction on the plurality of X-ray images such that the angles become substantially the same. A medical image processing apparatus according to claim 12.   The medical image processing apparatus according to claim 12, wherein the correction unit sets any one of the plurality of feature points as the reference point.   The medical image processing apparatus according to any one of claims 9, 12 and 13, wherein the correction unit sets a point based on a positional relationship between the plurality of feature points as the reference point. The acquisition unit sequentially acquires X-ray images acquired by the X-ray diagnostic apparatus,
The extraction unit sequentially extracts the regions in each of the plurality of acquired X-ray images,
The generation unit sequentially generates the plurality of feature points based on the extracted area.
The correction unit sequentially corrects the position of the plurality of X-ray images such that the reference points based on the plurality of generated feature points are substantially at the same position. The medical image processing device according to any one of the preceding claims. The acquisition unit stores the acquired plurality of X-ray images in a storage unit.
The extraction unit reads the plurality of X-ray images from the storage unit, and extracts the region in each of the plurality of read X-ray images.
The generation unit generates the plurality of feature points based on the extracted area.
The correction unit performs position correction on the plurality of X-ray images such that the reference points based on the plurality of generated feature points are substantially at the same position. The medical image processing apparatus according to any one of the preceding claims.   The extraction unit extracts, in each of the plurality of X-ray images, the region in which a tip region having a large mass per unit length is drawn out of the device. The medical image processing apparatus as described. An x-ray tube that generates x-rays,
An X-ray detector that detects X-rays emitted from the X-ray tube and outputs a detection signal according to the detected X-ray dose;
An acquisition unit configured to acquire a plurality of X-ray images based on the detection signal;
An extraction unit for extracting an area where the tip area of the device is depicted in each of the plurality of collected X-ray images;
A generation unit that generates a plurality of feature points based on the extracted area;
A correction unit that performs position correction on the plurality of X-ray images such that the reference points based on the plurality of generated feature points become substantially the same position;
An X-ray diagnostic apparatus comprising: Acquire multiple x-ray images,
In each of the plurality of acquired X-ray images, an area where the tip area of the device is depicted is extracted;
Generating a plurality of feature points based on the extracted area;
A medical image processing program that causes a computer to execute each process of correcting the position of the plurality of X-ray images so that the reference points based on the plurality of generated feature points become substantially the same position.

Images