JP6449383B2 - Medical image processing apparatus and X-ray diagnostic apparatus - Google Patents

Description

Embodiments of the present invention, a medical image processing apparatus, and relates to X-ray diagnostic equipment.

  Conventionally, when X-rays are detected by an X-ray image fluoroscopic imaging apparatus, X-rays scattered by a subject (hereinafter referred to as scattered rays) may enter a detector. A grid is used to prevent scattered radiation from entering the detector. FIG. 14 illustrates how X-rays generated from an X-ray tube are detected by a flat panel detector (hereinafter referred to as FPD). A direct line indicated by a one-dot chain line is an X-ray that does not pass through the subject P. Scattered rays indicated by dotted lines are X-rays that pass through the subject P and are scattered by the subject P at that time. Non-scattered rays that pass through the subject P indicated by solid lines are X-rays that pass through the subject P and are not scattered.

  For example, the grid has a pattern structure in which foils such as aluminum that transmits X-rays and foils such as lead that absorbs scattered X-rays are alternately arranged. As shown in FIG. 14, when X-ray imaging or X-ray fluoroscopy is performed with the grid placed on the X-ray incident surface of the detector, scattered radiation is removed by the grid. This makes it difficult for scattered rays to reach the detector. This reduces the dose of scattered radiation that reaches the detector. However, there are also scattered rays that reach the detector without being removed by the grid. The scattered radiation that has reached the detector is displayed as noise in an image (hereinafter referred to as a medical image) generated based on the output from the detector. For this reason, processing for reducing the scattered radiation component in the medical image is executed (hereinafter referred to as scattered radiation correction processing).

  Conventionally, as one of the scattered ray correction processes, there is a method of executing the scattered ray correction process by calculation in a frequency space. The Fourier transform of the image in which the scattered radiation component is reduced by the scattered radiation correction process (hereinafter referred to as a scattered radiation reduced image) is generated based on the Fourier transform of the medical image and the Fourier transform of the scattering function. Furthermore, the scattered radiation reduced image is generated by applying the inverse Fourier transform to the Fourier transform of the scattered radiation reduced image. However, with the above method, the scattering function cannot be changed according to the position of the pixel in the medical image. Therefore, for example, in a medical image including a direct line component, or in a medical image having a non-direct line component that has been transmitted through a partially thin portion (hereinafter referred to as a thin body portion) of the subject P, the scattered ray component is detected. It cannot be reduced appropriately. For example, there is a problem that the scattered radiation component is excessively corrected (hereinafter referred to as overcorrection).

  In order to solve the above problem, there is a method of generating a scattered radiation reduced image by repeatedly performing a predetermined number of times as described below. In this method, when the number of repetitions is the first, the first scattered radiation component is estimated based on the medical image. Here, the first scattered radiation component is calculated by multiplying the convolution sum of the plurality of pixel values and the scattering function in the medical image by the direct line ratio. The direct ray ratio is the ratio of the direct ray dose to the sum of the direct ray dose and the scattered ray dose in each pixel of the medical image. Next, a first scattered radiation reduced image is generated by subtracting the first scattered radiation component from the medical image.

  When the number of repetitions is the second time, the second scattered radiation component is estimated based on the first scattered radiation reduced image. Here, the second scattered radiation component is calculated by multiplying the convolution sum of the plurality of pixel values and the scattering function in the first scattered radiation reduced image by the direct line ratio. The direct ray ratio is the ratio of the direct ray dose to the sum of the direct ray dose and the scattered ray dose in each pixel of the first scattered ray reduced image. Next, a second scattered radiation reduced image is generated by subtracting the first scattered radiation component from the second scattered radiation component.

  That is, when the number of repetitions is n (n is a natural number equal to or greater than 2), the nth scattered radiation component is estimated based on the (n-1) th scattered radiation reduced image. Here, the n-th scattered radiation component is calculated by multiplying the convolution sum of the plurality of pixel values and the scattering function in the (n−1) -th scattered radiation reduced image by the direct line ratio. The direct ray ratio is the ratio of the direct ray dose to the sum of the direct ray dose and the scattered ray dose at the position of each of the (n−1) -th scattered ray reduced images. Next, an nth scattered radiation reduced image is generated by subtracting the (n−1) th scattered radiation component from the nth scattered radiation component. By repeating the above processing a predetermined number of times, a scattered radiation reduced image is generated.

  Usually, as the number of repetitions n increases, the accuracy of the scattered radiation correction processing improves. However, the above method has a problem that the amount of calculation increases because the number of convolution sums increases as the value of n increases. That is, the above method has a problem that it takes time to execute the scattered radiation correction process. For example, in X-ray fluoroscopy, there is a problem that display delay or frame dropping occurs and real-time display becomes difficult.

JP 2011-147615A

Meikle, Steven R., Brian F. Hutton, and Dale L. Bailey. "A transmission-dependent method for scatter correction in SPECT." Journal of nuclear medicine: official publication, Society of Nuclear Medicine 35.2 (1994): 360.

The purpose is to reduce the amount of calculation and to detect scattered radiation without overcorrection, even for medical images that have a direct line component and medical images that have a non-direct line component that has been transmitted through a thin part of the subject. the medical image processing apparatus capable of generating a reduced image, and to provide an X-ray diagnostic equipment.

The medical image processing apparatus according to the present embodiment includes a pixel value conversion unit that converts a pixel value higher than a reference value to a lower pixel value among a plurality of pixel values constituting a medical image, and the plurality of pixel values. one of the converted image converted by the pixel value converting unit, based on the scattering function, a scatter image generation unit that converts one of the scattered radiation image in the medical image, the one of the scattered radiation image from the medical image And a scattered radiation reduced image generating unit that generates a scattered radiation reduced image in which the scattered radiation is reduced by performing the difference.

FIG. 1 is a configuration diagram illustrating an example of a configuration of a medical image processing apparatus according to the first embodiment. FIG. 2 is a diagram illustrating an example of a distribution of a plurality of pixel values constituting a medical image according to the first embodiment. FIG. 3 is a diagram illustrating an example of a scattered radiation reduced image generated by applying the scattered radiation correction process to a medical image having a direct line component according to the first embodiment. FIG. 4 is a diagram illustrating an example of a scattered radiation reduced image generated by applying the scattered radiation correction process to a medical image that does not have a direct line component according to the first embodiment. FIG. 5 is a flowchart illustrating an example of the procedure of the scattered radiation correction process according to the first embodiment. FIG. 6 is a diagram illustrating an example of setting a region of interest in a medical image according to a modification of the first embodiment. FIG. 7 is a flowchart illustrating an example of a procedure of the scattered radiation correction process according to a modification of the first embodiment. FIG. 8 is a configuration diagram illustrating an example of the configuration of the X-ray diagnostic apparatus according to the second embodiment. FIG. 9 is a flowchart illustrating an example of the procedure of the scattered radiation correction process according to the second embodiment. FIG. 10 is a flowchart illustrating an example of the procedure of the scattered radiation correction process according to a modification of the second embodiment. FIG. 11 is a configuration diagram illustrating an example of a configuration of an X-ray computed tomography apparatus according to the third embodiment. FIG. 12 is a diagram illustrating an example of a sinogram in which the projection data values defined by the view angle and the channel number are represented by shading according to the third embodiment. FIG. 13 is a flowchart illustrating an example of a procedure of scattered radiation correction processing according to the third embodiment. FIG. 14 is a diagram according to the prior art.

  Hereinafter, a medical image processing apparatus 1 according to an embodiment will be described with reference to the drawings. In the following description, components having substantially the same function and configuration are denoted by the same reference numerals, and redundant description will be given only when necessary.

(First embodiment)
FIG. 1 shows a configuration of a medical image processing apparatus 1 according to the first embodiment. The medical image processing apparatus 1 includes an interface unit 3, a storage unit 5, a subject thickness determination unit 7, a scattering function determination unit 9, a reference value determination unit 11, a pixel value conversion unit 13, and a scattered radiation image generation. A unit 15, a scattered radiation reduced image generation unit 17, an input unit 19, a display unit 21, and a control unit 23.

The interface unit 3 is connected to a plurality of medical image diagnostic apparatuses via a network. The medical image diagnostic apparatus includes, for example, an X-ray diagnostic apparatus, an X-ray computed tomography (hereinafter referred to as CT), a magnetic resonance imaging (hereinafter referred to as MRI) apparatus, an ultrasonic diagnostic apparatus, and a nuclear Medical diagnostic apparatus (eg, Positron Emission Computed Tomography (hereinafter referred to as PET) apparatus, single photon emission computed tomography (Single Photon Emission Tomography)
(Computed Tomography: hereinafter referred to as SPECT) apparatus).

  The interface unit 3 outputs the medical image and the X-ray condition acquired from the medical image diagnostic apparatus to the storage unit 5 described later. The X-ray conditions are conditions such as a tube voltage, a tube current, a pulse time, and an irradiation field indicating an X-ray irradiation range in X-ray imaging and X-ray fluoroscopy. The interface unit 3 may appropriately output the medical image captured from the medical image diagnostic apparatus to the reference value determining unit 11, the pixel value converting unit 13, the scattered radiation reduced image generating unit 17, the display unit 21, and the like. .

  The storage unit 5 stores the X-ray conditions taken from the interface unit 3, medical images, operator instructions sent from the input unit 19 described later, and the like. Note that the X-ray conditions can be appropriately changed by the operator via the input unit 19 described later. The operator's instructions are various instructions, commands, information, selections, settings, etc. input by the operator at the input unit 19 described later. In addition, the memory | storage part 5 may memorize | store the program regarding the scattered radiation correction process mentioned later.

  The subject thickness determining unit 7 determines the subject thickness based on the X-ray conditions stored in the storage unit 5. X-ray conditions are conditions relating to the generation of X-rays such as tube voltage, tube current, and imaging time. The subject thickness determining unit 7 includes a memory (not shown), and stores, for example, a correspondence table of subject thicknesses with respect to tube voltages (hereinafter referred to as tube voltage body thickness correspondence tables). The tube voltage body thickness correspondence table may be a correspondence table of subject thicknesses with respect to elements other than the tube voltage (for example, tube current, tube current time product, etc.). Specifically, the subject thickness determining unit 7 determines the subject thickness based on the X-ray condition and the tube voltage body thickness correspondence table read from the storage unit 5. The subject thickness may be determined by an instruction from the operator via the input unit 19 described later.

  The scattering function determination unit 9 determines a scattering function based on the X-ray conditions stored in the storage unit 5 and the subject thickness determined by the subject thickness determination unit 7. The scatter function determination unit 9 includes a memory (not shown), and stores a scatter function correspondence table (hereinafter referred to as a scatter function correspondence table) with respect to the X-ray conditions and the object thickness. Note that the scattering function is a function corresponding to a scattered radiation component in a medical image. Specifically, the scattering function determination unit 9 determines the scattering function based on the subject thickness determined by the subject thickness determination unit 7, the X-ray conditions read from the storage unit 5, and the scattering function correspondence table. To do.

  The reference value determination unit 11 determines a reference value by multiplying a representative value of a plurality of pixel values constituting a medical image by a predetermined constant. The reference value determination unit 11 includes a memory (not shown) and stores a predetermined constant. The predetermined constant may be changed by an instruction from the operator via the input unit 19 described later. The predetermined constant will be described in detail later. The reference value determination unit 11 determines the mode value of a plurality of pixel values constituting the medical image and uses it as the representative value.

  In X-ray fluoroscopy or continuous X-ray imaging, the above-described processing of the subject thickness determination unit 7, the scattering function determination unit 9, and the reference value determination unit 11 is performed before X-ray fluoroscopy or continuous X-ray imaging. May be. The medical images used for each of the above processes are obtained via the interface unit 3 before X-ray fluoroscopy or continuous X-ray imaging.

  FIG. 2 is a diagram illustrating an example of a distribution (pixel value distribution) of a plurality of pixel values constituting a medical image. In the pixel value distribution, the direct line component is present in a higher pixel value range than the non-direct line component because there is no dose attenuation due to the transmission of the subject P.

  In addition, a non-direct line component that has partially transmitted through a thin portion (hereinafter referred to as a thin body portion) of the subject P is less attenuated due to the transmission of the subject P, like the direct line component. The pixel value is in a range higher than that of the non-direct line component. In order to make the description more specific, description will be made using medical images for the chest. In the medical image for the chest, the thickness of the chest is almost constant. However, a boundary portion between the subject P and the background or a portion such as an arm or a neck may be projected on the medical image. Since the above portion is thinner than the chest portion, dose attenuation due to transmission of the subject P is less than that of other non-direct line components. Therefore, the non-direct line component transmitted through the thin body thickness portion exists in a higher pixel value range than the other non-direct line components.

  Hereinafter, for the sake of simplicity, only a medical image having a direct line component will be described. The same effect can be obtained for a medical image having a non-direct line component that has passed through a thin thickness portion.

  The pixel value conversion unit 13 includes a memory (not shown) and stores a pixel value conversion table. The pixel value conversion table shows the correspondence between the pixel value before conversion and the pixel value after conversion. Based on the pixel value conversion table and the reference value, the pixel value conversion unit 13 converts a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. For example, the pixel value conversion unit 13 converts a pixel value of a pixel having a direct line component in a medical image into a low pixel value.

  Specifically, the pixel value conversion table represents, for example, the correspondence relationship between the pixel value before conversion and the pixel value after conversion as follows. The pixel value conversion unit 13 performs identity conversion on pixel values equal to or less than the reference value among the pixel values of the medical image. Note that the pixel value conversion unit 13 may leave the pixel values below the reference value among the pixel values of the medical image unchanged. The pixel value conversion unit 13 converts a pixel value that is not less than the reference value and not more than twice the reference value among the pixel values of the medical image into a pixel value that is not more than the reference value. The pixel value conversion unit 13 converts the pixel value of the medical image that is twice or more the reference value to 0. It should be noted that an image obtained by converting a pixel value of a medical image (hereinafter referred to as a converted image) by converting a pixel value that is greater than or equal to the reference value and twice or more the reference value to a lower pixel value will be described later. In the scattered radiation image generated by the scattered radiation image generating unit 15, the generation of artifacts can be suppressed.

  Hereinafter, for specific description, the pixel value conversion table having the above correspondence relationship is used as an example.

  Note that the pixel value conversion table is changed by changing the reference value in accordance with an instruction from an operator or the like in the input unit 19 described later. The reference value is changed by changing a predetermined constant. Details of the predetermined constant will be described later. Hereinafter, an image obtained by converting a pixel value of a medical image is referred to as a converted image.

  The scattered radiation image generation unit 15 converts the converted image obtained by converting the plurality of pixel values constituting the medical image by the pixel value conversion unit 13 into a scattered radiation image in the medical image based on the scattering function. Specifically, the scattered radiation image generation unit 15 generates a Fourier transform of the converted image. The scattered radiation image generator 15 generates a Fourier transform of the scattering function. The scattered radiation image generation unit 15 divides the Fourier transform of the scattering function by the sum of the Fourier transform of the scattering function and 1 (hereinafter, the result of the division is referred to as a scattering function term). The scattered radiation image generation unit 15 generates a Fourier transform of the scattered radiation image by multiplying the transformed image by the Fourier transform and the scattering function term.

  The scattered radiation image generation unit 15 generates a scattered radiation image by applying inverse Fourier transform to the Fourier transform of the scattered radiation image. Multiplying the Fourier transform of the transformed image and the scattering function term corresponds to changing the scattering function approximately in accordance with the position of the pixel of the medical image in real space. In other words, the scattered radiation image is an image in which the scattering function is approximately changed according to the position of the pixel of the medical image.

  The scattered radiation reduced image generation unit 17 generates a scattered radiation reduced image by subtracting the scattered radiation image from the medical image. The scattered radiation image generation unit 15 outputs the scattered radiation reduced image to the display unit 21. FIG. 3 is a diagram illustrating an example of a scattered radiation reduced image of a medical image having a direct line component. A region A in FIG. 3 is a pixel region containing a large amount of direct line components. As is apparent from FIG. 3, the scattered radiation correction process is appropriately executed even in the medical image having the direct line component by applying the scattered radiation correction process in the present embodiment. That is, the scattered radiation correction process is performed without excessive correction (hereinafter referred to as overcorrection). FIG. 4 is a diagram illustrating an example of a scattered radiation reduced image of a medical image that does not have a direct line component. As apparent from FIG. 4, the scattered radiation correction process is appropriately executed by applying the scattered radiation correction process according to the present embodiment even for a medical image having no direct line component.

  The input unit 19 inputs various instructions, commands, information, selections, settings, and the like from an operator or the like to the control unit 23 described later. Note that the input unit 19 may input a predetermined constant to the control unit 23 according to an operator's instruction. Based on the input, the control unit 23 updates a predetermined constant stored in the memory of the reference value determination unit 11. The predetermined constant is preferably a value that converts the pixel value of the direct line component into a low pixel value.

  The input unit 19 includes input devices such as a trackball, a switch button, a mouse, a mouse wheel, and a keyboard for inputting the various instructions, commands, information, selections, settings, and the like. The input device may be a touch panel that covers the display screen in the display unit 21. The input unit 19 can also input a region of interest on the medical image used in the reference value determination unit 11. For example, an operation for setting a region of interest is input by moving the mouse cursor on the medical image displayed on the display unit 21 and performing click, drag, or the like.

  The display unit 21 displays the scattered radiation reduced image generated by the scattered radiation reduced image generator 17. In addition, when inputting a region of interest, a medical image can be displayed.

  The control unit 23 includes a CPU (Central Processing Unit) and a memory (not shown). The control unit 23 temporarily stores information such as an operator instruction sent from the input unit 19 in a memory (not shown). In order to execute image processing in accordance with an operator instruction stored in the memory, the control unit 23 performs an object thickness determination unit 7, a scattering function determination unit 9, a reference value determination unit 11, a pixel value conversion unit 13, The scattered radiation image generation unit 15, the scattered radiation reduction image generation unit 17, and the like are controlled.

  FIG. 5 is a flowchart illustrating an example of the procedure of the scattered radiation correction process in the first embodiment.

  The X-ray condition is read from the storage unit 5 (step Sa1). The subject thickness is determined based on the X-ray condition (step Sa2). A scattering function is determined based on the object thickness and the X-ray condition (step Sa3). A reference value is determined by multiplying a representative value of a plurality of pixel values constituting a medical image that has been X-rayed or X-rayed by an X-ray condition by a predetermined constant (step Sa4). Among a plurality of pixel values constituting the medical image, a pixel value higher than the reference value is converted into a pixel value lower than the reference value (step Sa5). A scattered radiation image is generated based on the converted image obtained by converting the pixel values of the medical image and the scattering function (step Sa6). A scattered radiation reduced image is generated by subtracting the scattered radiation image from the medical image (step Sa7). A scattered radiation reduced image is displayed (step Sa8).

(Modification)
The difference from the first embodiment is that the reference value determination unit 11 determines the reference value based on the representative value of the pixel value included in the region of interest.

  The input unit 19 inputs a region of interest setting from an operator or the like to the control unit 23.

  The reference value determination unit 11 determines a reference value by using an average value or median value of a plurality of pixel values included in the region of interest input by the input unit 19 as a representative value. FIG. 6 is a diagram illustrating an example of setting a region of interest in a medical image.

  FIG. 7 is a flowchart illustrating an example of the procedure of the scattered radiation correction process in the modification of the first embodiment.

  A medical image is displayed on the display unit 21 (step Sb1). The region of interest input by the input unit 19 is stored in the storage unit 5 (step Sb2). The X-ray condition is read from the storage unit 5 (step Sb3). The subject thickness is determined based on the X-ray condition (step Sb4). A scattering function is determined based on the object thickness and the X-ray condition (step Sb5). A reference value is determined by multiplying a representative value of a plurality of pixel values included in the region of interest of the medical image X-rayed or X-rayed by the X-ray condition by a predetermined constant (step Sb6). Among a plurality of pixel values constituting the medical image, a pixel value higher than the reference value is converted into a pixel value lower than the reference value (step Sb7). A scattered radiation image is generated based on the converted image obtained by converting the pixel value of the medical image and the scattering function (step Sb8). A scattered radiation reduced image is generated by subtracting the scattered radiation image from the medical image (step Sb9). A scattered radiation reduced image is displayed (step Sb10).

  According to the configuration described above, the following effects can be obtained.

  According to the medical image processing apparatus 1 in the first embodiment, the reference value can be determined based on the medical image. Based on the pixel value conversion table and the reference value, the pixel value of each of the plurality of pixels constituting the medical image can be converted to generate a converted image. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. Further, the scattering function can be determined based on the X-ray condition and the subject thickness. According to the present embodiment, by using the converted image, the scattered radiation image can be generated by changing the scattering function according to the position of the pixel of the medical image. As a result, the scattered radiation image is generated by reducing the direct line component in the medical image. That is, by applying the scattered radiation correction processing in the present embodiment to a medical image having a direct line component, a scattered radiation reduced image can be generated without overcorrection.

  The non-direct line component that has passed through the thin body thickness portion has the same effect as the direct line component. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. Therefore, the scattered radiation image generated based on the converted image and the scattering function is generated by reducing the non-direct line component transmitted through the thin thickness portion in the medical image. That is, the scattered radiation reduced image can be generated without overcorrection by applying the scattered radiation correction processing in the present embodiment to the medical image having the thin body portion.

  Further, according to the modification of the first embodiment, the reference value can be determined based on the region of interest on the input medical image. The reference value is a median value or an average value of a plurality of pixel values included in the region of interest. Based on the determined reference value, the pixel value of each of a plurality of pixels constituting the medical image can be converted to generate a converted image. That is, by applying the scattered radiation correction processing in the present embodiment to the medical image in which the region of interest is set based on the pixel values of each of the plurality of pixels included in the region of interest, the scattered radiation reduced image without overcorrection. Can be generated.

  From the above, according to the medical image processing apparatus 1 in the first embodiment, a non-direct line component that has transmitted a medical image including a direct line and a partially thin portion (thin body thickness portion) of the subject. Even in the case of medical images having the above, it is possible to reduce the amount of calculation and generate a scattered radiation reduced image without overcorrection.

(Second Embodiment)
FIG. 8 is a configuration diagram showing an example of the configuration of the X-ray diagnostic apparatus 25 according to the second embodiment. The X-ray diagnostic apparatus 25 includes an X-ray generation unit 27, an X-ray detection unit 29, a support mechanism 31, a support mechanism drive unit 33, a medical image generation unit 37, an interface unit 3, a storage unit 5, Object thickness determination unit 7, scattering function determination unit 9, reference value determination unit 11, pixel value conversion unit 13, scattered radiation image generation unit 15, scattered radiation reduction image generation unit 17, and input unit 19 The display unit 21 and the control unit 23 are included.

  The X-ray generator 27 has an X-ray tube and a high voltage generator (not shown). The high voltage generator generates a tube current supplied to the X-ray tube and a tube voltage applied to the X-ray tube. The high voltage generator supplies a tube current suitable for X-ray imaging or fluoroscopy to the X-ray tube, and applies a tube voltage suitable for X-ray imaging or X-ray fluoroscopy to the X-ray tube. The X-ray tube generates X-rays from the X-ray focal point (hereinafter referred to as the tube focal point) based on the tube current supplied from the high voltage generator and the tube voltage applied by the high voltage generator. To do.

  The X-ray detector 29 detects X-rays generated by the X-ray generator 27 and transmitted through the subject P. The X-ray detection unit 29 detects X-rays generated by the X-ray generation unit 27. The X-ray detection unit 29 includes, for example, a flat panel detector (hereinafter referred to as FPD). The FPD has a photoelectric conversion film that converts light into an electrical signal. The FPD converts incident X-rays into electric signals by a photoelectric conversion film. An electrical signal generated by the photoelectric conversion film is output to an analog-to-digital converter (hereinafter referred to as an A / D converter) (not shown). The A / D converter converts an electrical signal into digital data. The A / D converter outputs the digital data to a preprocessing unit (not shown). The X-ray detection unit 29 arranges a grid in front of the X-ray incident surface in the FPD. Note that the X-ray detection unit 29 may include an image intensifier.

  The support mechanism 31 supports the X-ray generation unit 27 and the X-ray detection unit 29 so as to be movable. Specifically, the support mechanism 31 includes, for example, a C arm and a C arm support unit (not shown). The C-arm mounts the X-ray generator 27 and the X-ray detector 29 so as to face each other. An Ω arm or the like may be used instead of the C arm. The X-ray diagnostic apparatus 25 may be a digestive tract imaging apparatus, a chest imaging apparatus, a mammography apparatus, or the like that does not have an arm.

  The support mechanism drive unit 33 drives the support mechanism 31 under the control of the control unit 23 described later. Specifically, the support mechanism drive unit 33 supplies a drive signal corresponding to a control signal from the control unit 23 to the C arm support unit, and slides and rotates the C arm in a predetermined direction. At the time of X-ray imaging or X-ray fluoroscopy, the subject P placed on the top board 35 is disposed between the X-ray generation unit 27 and the X-ray detection unit 29.

  A top plate drive unit (not shown) moves the top plate 35 by driving the top plate 35 under the control of the control unit 23 described later. Specifically, the top plate driving unit is configured to, based on a control signal from the control unit 23, the short axis direction of the top plate 35 (X direction in FIG. 8) or the long axis direction of the top plate 35 (Y direction in FIG. 8). Then, the top plate 35 is slid. Further, the top plate driving unit moves the top plate 35 up and down in the vertical direction (Z direction in FIG. 8). In addition, the top plate driving unit rotates the top plate 35 to tilt the top plate 35 with at least one of the major axis direction and the minor axis direction as a rotation axis (X axis, Y axis in FIG. 8). May be.

  A preprocessing unit (not shown) performs preprocessing on the digital data output from the X-ray detection unit 29. The preprocessing includes correction of non-uniform sensitivity between channels in the X-ray detection unit 29, correction regarding dropout, and the like. The preprocessed digital data is output to a medical image generation unit 37 described later.

  The medical image generation unit 37 generates a medical image based on the processed digital data. The medical image generation unit 37 appropriately outputs the medical image to the reference value determination unit 11, the pixel value conversion unit 13, the scattered radiation reduced image generation unit 17, and the display unit 21. The medical image generation unit 37 may output the generated medical image to the storage unit 5 described later.

  The interface unit 3 may output a medical image captured from the medical image diagnostic apparatus to the storage unit 5 described later. The interface unit 3 transfers the medical image and the X-ray condition acquired from another medical image diagnostic apparatus to the reference value determination unit 11, the pixel value conversion unit 13, the scattered radiation reduced image generation unit 17, the display unit 21, and the like. You may output suitably.

  The storage unit 5 stores an operator's instruction and the like sent from the input unit 19 described later. The storage unit 5 stores the X-ray conditions input by an operator's instruction in the input unit 19 described later. The storage unit 5 may store the X-ray conditions acquired from the interface unit 3. The storage unit 5 may store a medical image acquired from the medical image generation unit 37 or a medical image acquired from the interface unit 3. The memory | storage part 5 may memorize | store the program regarding the scattered-radiation correction process mentioned later.

  The subject thickness determining unit 7 determines the subject thickness based on the X-ray conditions stored in the storage unit 5. The subject thickness determining unit 7 includes a memory (not shown) and stores a tube voltage body thickness correspondence table. Specifically, the subject thickness determining unit 7 determines the subject thickness based on the X-ray condition and the tube voltage body thickness correspondence table read from the storage unit 5.

  The scattering function determination unit 9 determines a scattering function based on the X-ray conditions stored in the storage unit 5 and the subject thickness determined by the subject thickness determination unit 7. The scattering function determination unit 9 includes a memory (not shown) and stores a scattering function correspondence table. Specifically, the scattering function determination unit 9 determines the scattering function based on the subject thickness determined by the subject thickness determination unit 7, the X-ray conditions read from the storage unit 5, and the scattering function correspondence table. To do.

  The reference value determination unit 11 determines a reference value by multiplying a representative value of a plurality of pixel values constituting a medical image by a predetermined constant.

  The pixel value conversion unit 13 includes a memory (not shown) and stores a pixel value conversion table. Based on the pixel value conversion table and the reference value, the pixel value conversion unit 13 converts a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. For example, the pixel value conversion unit 13 converts a pixel value of a pixel having a direct line component in a medical image into a low pixel value.

  The scattered radiation image generation unit 15 generates a scattered radiation image based on the converted image converted by the pixel value conversion unit 13 and the scattering function determined by the scattering function determination unit 9. Specifically, the scattered radiation image generation unit 15 generates a Fourier transform of the converted image. The scattered radiation image generator 15 generates a Fourier transform of the scattering function. The scattered radiation image generation unit 15 divides the Fourier transform of the scattering function by the sum of the Fourier transform of the scattering function and 1 (a scattering function term). The scattered radiation image generation unit 15 generates a Fourier transform of the scattered radiation image by multiplying the transformed image by the Fourier transform and the scattering function term. The scattered radiation image generation unit 15 generates a scattered radiation image by applying inverse Fourier transform to the Fourier transform of the scattered radiation image.

  The scattered radiation reduced image generator 17 generates a scattered radiation reduced image by subtracting the scattered radiation image determined by the scattered radiation image generator 15 from the medical image. The scattered radiation image generation unit 15 outputs the scattered radiation reduced image to the display unit 21.

  The input unit 19 displays the X-ray conditions desired by the operator, the X-ray imaging position, the X-ray fluoroscopic position, the start and end of X-ray imaging or X-ray fluoroscopy, the display of the projection image, and the display of a plurality of cross-sectional images Enter the switching to be displayed. The input unit 19 inputs various instructions, commands, information, selections, settings, and the like from an operator or the like to the control unit 23 described later. Note that the input unit 19 may input a predetermined constant to the control unit 23 according to an operator's instruction. Based on the input, the control unit 23 updates a predetermined constant stored in the memory of the reference value determination unit 11.

  The input unit 19 includes input devices such as a trackball, a switch button, a mouse, a mouse wheel, and a keyboard for inputting the various instructions, commands, information, selections, settings, and the like. The input device may be a touch panel that covers the display screen in the display unit 21. The input unit 19 can also input a region of interest on the medical image used in the reference value determination unit 11. For example, an operation for setting a region of interest is input by moving the mouse cursor on the medical image displayed on the display unit 21 and performing click, drag, or the like.

  The display unit 21 displays the scattered radiation reduced image generated by the scattered radiation reduced image generator 17. The display unit 21 can also display a medical image when setting the region of interest.

  The control unit 23 includes a CPU and a memory (not shown). The control unit 23 temporarily stores information such as an operator instruction sent from the input unit 19 in a memory (not shown). The control unit 23 performs an X-ray diagnosis in accordance with an operator instruction stored in the memory and the like, in order to perform an X-ray diagnosis, an X-ray generation unit 27, a scattering function determination unit 9, a pixel value conversion unit 13, and a scattered radiation image generation unit 15. The scattered radiation reduced image generator 17 and the like are controlled.

  FIG. 9 is a flowchart illustrating an example of the procedure of the scattered radiation correction process in the second embodiment.

  An X-ray condition is input at the input unit 19 (step Sc1). The subject thickness is determined based on the input X-ray condition (step Sc2). A scattering function is determined based on the object thickness and the X-ray condition (step Sc3). A reference value is determined by multiplying a representative value of a plurality of pixel values constituting a medical image that has been X-rayed or X-rayed by an X-ray condition by a predetermined constant (step Sc4). Among a plurality of pixel values constituting the medical image, a pixel value higher than the reference value is converted into a pixel value lower than the reference value (step Sc5). A scattered radiation image is generated based on the converted image obtained by converting the pixel values of the medical image and the scattering function (step Sc6). A scattered radiation reduced image is generated by subtracting the scattered radiation image from the medical image (step Sc7). A scattered radiation reduced image is displayed (step Sc8).

(Modification)
The difference from the second embodiment is that the processing described below is executed. By imaging the subject P before X-ray fluoroscopy or continuous X-ray imaging (hereinafter referred to as first imaging), a medical image relating to the first imaging (hereinafter referred to as first medical image) is generated. Further, a reference value is determined based on the first medical image. In addition, based on the determined reference value, scattering is performed on a medical image (hereinafter referred to as a second medical image) generated by fluoroscopy or continuous X-ray imaging (hereinafter referred to as second imaging). Line correction processing is executed.

  The X-ray generator 27 generates X-rays from the tube focus in the first imaging. The X-ray generator 27 generates X-rays from the tube focus in the second imaging.

  The X-ray detector 29 detects X-rays generated from the X-ray generator 27 and transmitted through the subject P in the first imaging. The X-ray detector 29 detects X-rays generated from the X-ray generator 27 and transmitted through the subject P in the second imaging.

  A preprocessing unit (not shown) performs preprocessing on digital data (hereinafter referred to as first digital data) output from the X-ray detection unit 29 by the first imaging. The preprocessed first digital data is output to a medical image generation unit 37 described later. A preprocessing unit (not shown) performs preprocessing on digital data (hereinafter referred to as second digital data) output from the X-ray detection unit 29 by the second imaging. The preprocessed second digital data is output to a medical image generation unit 37 described later.

  The medical image generation unit 37 generates a first medical image based on the preprocessed first digital data. The medical image generation unit 37 outputs the first medical image to the reference value determination unit 11. The medical image generation unit 37 generates a second medical image based on the second digital data by the second imaging. The medical image generation unit 37 outputs the second medical image to the pixel value conversion unit 13 and the scattered radiation reduced image generation unit 17. Note that the first and second medical images may be stored in the storage unit 5.

  The reference value determination unit 11 determines a reference value obtained by multiplying a representative value of a plurality of pixel values constituting the first medical image by a predetermined constant.

  The pixel value conversion unit 13 includes a memory (not shown) and stores a pixel value conversion table. Based on the pixel value conversion table and the reference value, the pixel value conversion unit 13 converts a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the second medical image. The pixel value conversion unit 13 converts the pixel value of the second medical image generated by the medical image generation unit 37 based on the pixel value conversion table and the reference value. Hereinafter, an image obtained by converting the pixel value of the second medical image is referred to as a converted image.

  The scattered radiation image generation unit 15 generates a scattered radiation image based on the converted image and the scattering function. Specifically, the scattered radiation image generation unit 15 generates a Fourier transform of the converted image. The scattered radiation image generator 15 generates a Fourier transform of the scattering function. The scattered radiation image generation unit 15 divides the Fourier transform of the scattering function by the sum of the Fourier transform of the scattering function and 1 (a scattering function term). The scattered radiation image generation unit 15 generates a Fourier transform of the scattered radiation image by multiplying the transformed image by the Fourier transform and the scattering function term. The scattered radiation image generation unit 15 generates a scattered radiation image by applying inverse Fourier transform to the Fourier transform of the scattered radiation image.

  The scattered radiation reduced image generator 17 generates a scattered radiation reduced image by subtracting the scattered radiation image from the second medical image generated by the medical image generator 37. The scattered radiation reduced image generation unit 17 outputs the scattered radiation reduced image to the display unit 21.

  The display unit 21 displays the scattered radiation reduced image generated by the scattered radiation reduced image generator 17.

  Note that, in X-ray fluoroscopy or continuous imaging, an X-ray generation unit 27, an X-ray detection unit 29, a pre-processing unit (not shown), a medical image generation unit 37, a pixel value conversion unit 13, a scattered radiation image generation unit 15, The processes of the scattered radiation reduced image generation unit 17 and the display unit 21 may be executed a plurality of times.

  FIG. 10 is a flowchart illustrating an example of the procedure of the scattered radiation correction process in the second embodiment.

  The input unit 19 inputs X-ray conditions (step Sd1). The subject thickness is determined based on the input X-ray condition (step Sd2). A scattering function is determined based on the object thickness and the X-ray condition (step Sd3). In the first imaging, a first medical image is generated (step Sd4). A reference value is determined by multiplying a representative value of a plurality of pixel values constituting the first medical image by a predetermined constant (step Sd5). Second imaging is started (step Sd6). The medical image generation unit 37 generates a second medical image (step Sd7). Among a plurality of pixel values constituting the second medical image, a pixel value higher than the reference value is converted into a pixel value lower than the reference value (step Sd8). A scattered radiation image is determined based on the converted image obtained by converting the pixel values of the second medical image and the scattering function (step Sd9). A scattered radiation reduced image is generated by subtracting the scattered radiation image from the second medical image (step Sd10). A scattered radiation reduced image is displayed (step Sd11). If the second shooting end instruction is input, the process ends. If not, the process returns to step Sd7 (step Sd12).

  According to the configuration described above, the following effects can be obtained.

  According to the X-ray diagnostic apparatus 25 in the second embodiment, the reference value can be determined based on the medical image. Based on the pixel value conversion table and the reference value, the pixel value of each of the plurality of pixels constituting the medical image can be converted to generate a converted image. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. Further, the scattering function can be determined based on the X-ray condition and the subject thickness. According to the present embodiment, by using the converted image, the scattered radiation image can be generated by changing the scattering function according to the position of the pixel of the medical image. As a result, the scattered radiation image is generated by reducing the direct line component in the medical image. That is, by applying the scattered radiation correction processing in the present embodiment to a medical image having a direct line component, a scattered radiation reduced image can be generated without overcorrection.

  The non-direct line component that has passed through the thin body thickness portion has the same effect as the direct line component. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the medical image. Therefore, the scattered radiation image generated based on the converted image and the scattering function is generated by reducing the non-direct line component transmitted through the thin thickness portion in the medical image. That is, the scattered radiation reduced image can be generated without overcorrection by applying the scattered radiation correction processing in the present embodiment to the medical image having the thin body portion.

  Further, according to the modification of the second embodiment, in the X-ray fluoroscopy or continuous X-ray imaging, the reference value is determined based on the first medical image captured before the X-ray fluoroscopy or continuous X-ray imaging. be able to. Based on the pixel value conversion table and the reference value, the pixel value of each of the plurality of pixels constituting the second medical image can be converted to generate a converted image. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the second medical image. Further, the scattering function can be determined based on the X-ray condition and the subject thickness. A scattered radiation image can be generated based on the converted image and the scattering function. The scattered radiation image is generated by reducing the direct line component in the second medical image. Accordingly, a scattered radiation reduced image can be generated without overcorrection even in the second medical image having a direct line component.

  The non-direct line component that has passed through the thin body thickness portion has the same effect as the direct line component. The converted image is obtained by converting a pixel value higher than the reference value to a pixel value lower than the reference value among a plurality of pixel values constituting the second medical image. Therefore, the scattered radiation image generated based on the converted image and the scattering function is generated by reducing the non-direct line component transmitted through the thin body thickness portion in the second medical image. Therefore, a scattered radiation reduced image can be generated without overcorrection in the second medical image having a non-direct line component transmitted through the thin body thickness portion.

  From the above, according to the X-ray diagnostic apparatus 25 in the second embodiment, a non-directly transmitted medical image having a direct line component and a partially thin portion (thin body thickness portion) of the subject P. Even for a medical image having a line component, the amount of calculation can be reduced and a scattered radiation reduced image can be generated without overcorrection.

(Third embodiment)
FIG. 11 is a configuration diagram illustrating an example of a configuration of an X-ray computed tomography apparatus 39 according to the third embodiment. The X-ray computed tomography apparatus 39 includes a gantry 41, a projection data generation unit 65, a storage unit 5, an object thickness determination unit 7, a scattering function determination unit 9, a reference value determination unit 11, and a projection data value. The conversion unit 67, the scattered radiation data generation unit 69, the scattered radiation reduction projection data generation unit 71, the reconstruction unit 73, the input unit 19, the display unit 21, and the control unit 23 are included.

  The gantry 41 accommodates a rotation support mechanism 43. The rotation support mechanism 43 includes a rotation ring (not shown), a ring support mechanism (not shown) that supports the rotation ring so as to be rotatable about the rotation axis Z, and a rotation drive unit 45 (electric motor) that drives the rotation of the rotation ring. ). The rotation support mechanism 43 includes a high voltage generator 47, an X-ray tube 49, a collimator unit 51, an X-ray detector 53, also referred to as a two-dimensional array type or a multi-row type, and a data acquisition system (Data Acquisition System). : Hereinafter referred to as DAS 57), a non-contact data transmission unit 59, a cooling device and a gantry control device (not shown), and the like.

  The high voltage generator 47 supplies the tube voltage applied to the X-ray tube 49 and the X-ray tube 49 using the power supplied via the slip ring 61 under the control of the control unit 23 described later. Tube current. The high voltage generator 47 applies the generated tube voltage to the X-ray tube 49. The high voltage generator 47 supplies the generated tube current to the X-ray tube 49.

  The X-ray tube 49 receives the application of the tube voltage from the high voltage generator 47 and the supply of the tube current, and emits X-rays from the X-ray focal point.

  X-rays emitted from the X-ray focal point are shaped into, for example, a cone beam shape (pyramidal shape) by a collimator unit 51 attached to the X-ray emission window of the X-ray tube 49. The X-ray emission range 63 is indicated by a dotted line. The X axis is a straight line that is orthogonal to the rotation axis Z and passes through the focal point of the emitted X-ray. The Y axis is a straight line orthogonal to the X axis and the rotation axis Z. For convenience of explanation, the XYZ coordinate system will be described as a rotating coordinate system that rotates about the rotation axis Z.

  The X-ray detector 53 is attached to the rotating ring at a position and an angle facing the X-ray tube 49 across the rotation axis Z. The X-ray detector 53 has a plurality of X-ray detection elements. Here, it is assumed that a single X-ray detection element constitutes a single channel. The plurality of channels are perpendicular to the rotation axis Z and centered on the focal point of the radiated X-ray, and the arc direction (channel) having a radius from this center to the center of the light receiving portion of the X-ray detection element for one channel. Direction) and the Z direction.

  The X-ray detector 53 may be composed of a plurality of modules in which a plurality of X-ray detection elements are arranged in a line. At this time, the modules are arranged one-dimensionally in a substantially arc direction along the channel direction.

  Further, the plurality of X-ray detection elements may be two-dimensionally arranged in two directions of the channel direction and the slice direction. That is, the two-dimensional arrangement is configured by arranging a plurality of channels arranged in a one-dimensional manner along the channel direction in a plurality of rows in the slice direction. The X-ray detector 53 having such a two-dimensional X-ray detection element arrangement may be configured by arranging a plurality of the above-described modules arranged in a one-dimensional shape in a substantially arc direction in a plurality of rows in the slice direction.

  During imaging or scanning, the subject P is placed on the top plate 35 and inserted into a cylindrical imaging region 55 between the X-ray tube 49 and the X-ray detector 53. A DAS 57 is connected to the output side of the X-ray detector 53.

  The DAS 57 includes an IV converter that converts a current signal of each channel of the X-ray detector 53 into a voltage, an integrator that periodically integrates the voltage signal in synchronization with an X-ray exposure period, An amplifier that amplifies the output signal of the integrator and an analog / digital converter that converts the output signal of the amplifier into a digital signal are attached to each channel. Data output from the DAS 57 (pure raw data) is transmitted to a projection data generation unit 65 (to be described later) via a non-contact data transmission unit 59 using magnetic transmission / reception or optical transmission / reception.

  The projection data generation unit 65 performs preprocessing on the pure raw data output from the DAS 57 to generate projection data (raw data). The preprocessing includes, for example, sensitivity non-uniformity correction processing between channels, X-ray strong absorber, processing for correcting signal signal drop or signal loss due to extreme metal intensity mainly. The projection data is stored in the storage unit 5 including a magnetic disk, a magneto-optical disk, or a semiconductor memory in association with data representing a view angle when data is collected.

  The projection data is a set of data values corresponding to the intensity of X-rays that have passed through the subject. Here, for convenience of explanation, a set of projection data over all channels having the same view angle collected almost simultaneously in one shot is referred to as a projection data set. Further, the view angle is expressed as an angle in a range of 360 ° with each position of the circular orbit around which the X-ray tube 49 circulates about the rotation axis Z as the top of the circular orbit vertically upward from the rotation axis Z being 0 °. It is a thing. For example, on the circular orbit, −90 ° and 270 ° at the same position on the circular orbit are the same view angle. On the circular orbit, 450 ° and 90 ° having the same position on the circular orbit are the same view angle. That is, n ° and (n ± 360) ° are the same view angle. The projection data for each channel of the projection data set is identified by the view angle, cone angle, and channel number.

  The storage unit 5 stores the projection data set generated by the projection data generation unit 65, the scattered radiation data set, and the scattered radiation reduction projection data set. The storage unit 5 stores an operator's instruction and the like sent from the input unit 19 described later. The storage unit 5 stores the X-ray conditions acquired from the interface unit 3. Note that the storage unit 5 may store a predetermined threshold value.

  The subject thickness determination unit 7 is based on a projection data set corresponding to a view that is 90 ° different from the views generated from the projection data generation unit 65 (hereinafter referred to as “subject thickness determination view”). Determine specimen thickness.

  FIG. 12 is a diagram showing an example of a sinogram in which projection data values defined by a view angle and a channel number are represented by shading. FIG. 12 shows that when determining a subject having a view angle i °, a projection data set corresponding to a view angle of (i−90) ° or (i + 90) ° with a view angle different by 90 ° is used. The subject thickness determining unit 7 determines the subject thickness A or the subject thickness B indicated by the bidirectional arrow in FIG. 12 as the subject thickness. Specifically, for example, the subject thickness determination unit 7 starts from the smallest channel number among a plurality of channels corresponding to projection data values larger than a predetermined threshold in a projection data set of a view that is 90 ° different from the target view. The subject thickness is determined based on the distance between the largest channel number. Specifically, the subject thickness determining unit 7 determines the subject thickness by dividing the distance from the smallest channel number to the largest channel number by the enlargement ratio. The enlargement ratio is determined based on the distance between the tube focus and the subject and the distance between the tube focus and the subject. The subject thickness determining unit 7 may determine the subject thickness based on an average value of the subject thickness A and the subject thickness B or the like.

  If there is no subject thickness determination view for the target view, the subject thickness determination unit 7 uses the projection data generation unit 65 to generate a projection data set corresponding to the subject thickness determination view using an interpolation method or the like. generate. The projection data generation unit 65 outputs a projection data set corresponding to the subject thickness determination view to the subject thickness determination unit 7. The subject thickness determination unit 7 determines the subject thickness based on the projection data set corresponding to the subject thickness determination view.

  The scattering function determination unit 9 determines a scattering function for each view based on the subject thickness determined by the subject thickness determination unit 7 and the X-ray conditions stored in the storage unit 5. The scattering function determination unit 9 includes a memory (not shown) and stores a scattering function correspondence table. Specifically, the scatter function determination unit 9 determines the view based on the object thickness for each view determined by the object thickness determination unit 7, the X-ray condition read from the storage unit 5, and the scatter function correspondence table. Determine the scattering function for each.

  The reference value determining unit 11 multiplies a representative value of a plurality of projection data values constituting each projection data set by a predetermined constant to determine a reference value for each view. The reference value determination unit 11 includes a memory (not shown) and stores a predetermined constant.

  The projection data value conversion unit 67 includes a memory (not shown) and stores a projection data value conversion table. The projection data value conversion table shows the correspondence between the projection data value before conversion and the projection data value after conversion. Based on the projection data value conversion table and the reference value for each view, the projection data value conversion unit 67 selects a projection data value higher than the reference value among the plurality of projection data values constituting the projection data set from the reference value. Convert to lower projection data values. For example, the projection data value conversion unit 67 converts a projection data value having a direct line component in the projection data set to a low projection data value. Hereinafter, the projection data value of the projection data set converted by the projection data value conversion unit 67 is referred to as a conversion data set.

  The scattered radiation data generation unit 69 converts each of the conversion data sets obtained by converting the plurality of projection data values constituting the projection data set by the projection data value conversion unit, based on the scattering function for each view, and the scattered radiation corresponding to each view. Convert to dataset. Specifically, the scattered radiation data generation unit 69 generates a Fourier transform of the transform data set for each view. The scattered radiation data generation unit 69 generates a Fourier transform of the scattering function for each view. The scattered radiation data generation unit 69 divides the Fourier transform of the scattering function by the sum of the Fourier transform of the scattering function and 1 for each view (scattering function term). The scattered radiation data generating unit 69 generates a Fourier transform of the scattered radiation data set for each view by multiplying the Fourier transform of the transformation data set by the scattering function term for each view. The scattered radiation data generation unit 69 generates a scattered radiation data set for each view by applying inverse Fourier transform to the Fourier transform of the scattered radiation data set for each view. Note that as many scattered data sets as the number of views are generated.

  The scattered radiation reduced projection data generation unit 71 generates a scattered radiation reduced projection data set with reduced scattered radiation for each view by subtracting the scattered radiation data set from the projection data set for each view. Note that as many scattered radiation reduced projection data sets as the number of views are generated. The scattered radiation reduction projection data generation unit 71 outputs the scattered radiation reduction projection data set to the display unit 21.

  The reconstruction unit 73 reconstructs substantially cylindrical volume data based on a scattered radiation reduced projection data set with a view angle in the range of 360 ° or 180 ° + fan angle. The reconstructed image is stored in the storage unit 5.

  The input unit 19 inputs various instructions, commands, information, selections, settings, and the like from an operator or the like to the control unit 23 described later. Note that the input unit 19 may input a predetermined constant to the control unit 23 according to an operator's instruction. Based on the input, the control unit 23 updates a predetermined constant stored in the memory of the reference value determination unit 11.

  The input unit 19 includes input devices such as a trackball, a switch button, a mouse, a mouse wheel, and a keyboard for inputting the various instructions, commands, information, selections, settings, and the like. The input device may be a touch panel that covers the display screen in the display unit 21.

  The display unit 21 displays the scattered radiation reduced projection data set generated by the scattered radiation reduced projection data generating unit 71.

  The control unit 23 includes a CPU and a memory (not shown). The control unit 23 temporarily stores information such as an operator instruction sent from the input unit 19 in a memory (not shown). The control unit 23 executes the image processing in accordance with the operator's instruction stored in the memory, etc., so that the subject thickness determination unit 7, the scattering function determination unit 9, the reference value determination unit 11, and the projection data value conversion unit 67 are performed. The scattered radiation data generator 69, the scattered radiation reduction projection data generator 71, and the like are controlled.

  FIG. 13 is a flowchart illustrating an example of the procedure of the scattered radiation correction process in the third embodiment.

  A plurality of projection data sets respectively corresponding to a plurality of views in one scan are generated (step Se1). A subject thickness for each view is determined based on a projection data set corresponding to 90 ° views of the views (Step Se2). A scattering function is determined based on the object thickness and the X-ray condition (step Se3). A reference value for each projection data set is determined by multiplying a representative value of a plurality of projection data values constituting each projection data set by a predetermined constant (step Se4). Using the reference value corresponding to each projection data set, a projection data value higher than the reference value among the projection data values is converted into a projection data value lower than the reference value (step Se5). Each of the converted projection data sets is converted based on the scattering function for each view to convert a plurality of scattered radiation projection data sets corresponding to each view (step Se6). By subtracting the scattered radiation data set for each view from the projection data set, a plurality of scattered radiation reduced projection data sets with reduced scattered radiation are generated (step Se7). Volume data is reconstructed based on the scattered radiation reduced projection data set (step Se8).

  According to the configuration described above, the following effects can be obtained.

  According to the X-ray computed tomography apparatus 39 in the third embodiment, the subject thickness for each view is determined based on a projection data set corresponding to a view that is 90 ° different from the view. The scattering function can be determined based on the object thickness and the X-ray condition. A reference value for each projection data set can be determined based on a representative value of a plurality of projection data values constituting each projection data set. A plurality of projection data values can be transformed using a reference value corresponding to each projection data set to generate a transformed projection data set. The converted projection data set is obtained by converting a projection data value higher than the reference value into a projection data value lower than the reference value among a plurality of projection data values constituting the projection data set. According to the present embodiment, by using the conversion data set, the scattered radiation data set can be generated by changing the scattering function according to the data number of the projection data set. Thereby, the scattered radiation data set is generated by reducing the direct line component in the projection data set. That is, by applying the scattered radiation correction processing in the present embodiment to a projection data set having a direct line component, a scattered radiation reduced projection data set can be generated without overcorrection. Therefore, by reconstructing the scattered radiation reduction projection data set, it is possible to generate volume data that has been subjected to the scattered radiation reduction processing without overcorrection.

  The non-direct line component that has passed through the thin body thickness portion has the same effect as the direct line component. The converted projection data set is obtained by converting a projection data value higher than the reference value into a projection data value lower than the reference value among a plurality of projection data values constituting the projection data set. Therefore, the scattered radiation data set generated based on the converted projection data set and the scattering function is generated by reducing the non-direct line component transmitted through the thin body thickness portion in the projection data set. That is, by applying the scattered radiation correction processing in the present embodiment to the projection data set having a non-direct line component that has passed through the thin body thickness portion, the scattered radiation reduced projection data set can be generated without overcorrection. Therefore, by reconstructing the scattered radiation reduction projection data set, it is possible to generate volume data that has been subjected to the scattered radiation reduction processing without overcorrection.

  In addition, each function according to the embodiment can also be realized by installing a scattered radiation correction processing program in a computer such as a workstation and developing these on a memory. At this time, a program capable of causing the computer to execute the method is stored in a storage medium such as a magnetic disk (floppy (registered trademark) disk, hard disk, etc.), an optical disk (CD-ROM, DVD, etc.), or a semiconductor memory. It can also be distributed.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other 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 scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

  DESCRIPTION OF SYMBOLS 1 ... Medical image processing apparatus, 3 ... Interface part, 5 ... Memory | storage part, 7 ... Subject thickness determination part, 9 ... Scattering function determination part, 11 ... Reference value determination part, 13 ... Pixel value conversion part, 15 ... Scattered ray Image generation unit 17 ... Scattered ray reduction image generation unit, 19 ... input unit, 21 ... display unit, 23 ... control unit, 25 ... X-ray diagnostic apparatus, 27 ... X-ray generation unit, 29 ... X-ray detection unit, 31 DESCRIPTION OF SYMBOLS ... Support mechanism, 33 ... Support mechanism drive part, 35 ... Top plate, 37 ... Medical image generation part, 39 ... X-ray computed tomography apparatus, 41 ... Gantry, 43 ... Rotation support mechanism, 45 ... Rotation drive part, 47 ... High voltage generator, 49 ... X-ray tube, 51 ... Collimator unit, 53 ... X-ray detector, 55 ... Imaging region, 57 ... DAS, 59 ... Non-contact data transmission unit, 61 ... Slip ring, 63 ... Radiation range , 65 ... projection data generation unit, 67 ... projection data value Section, 69 ... scattered radiation data generator, 71 ... scattered ray reduction projection data generation unit, 73 ... reconstruction unit.

Claims (9)

Among a plurality of pixel values constituting a medical image, a pixel value conversion unit that converts a pixel value higher than a reference value to a lower pixel value;
One of the converted image converted by said plurality of pixel value the pixel value converting unit, based on the scattering function, a scatter image generation unit that converts one of the scattered radiation image in the medical image,
A scattered radiation reduced image generator that generates a scattered radiation reduced image by reducing the scattered radiation by subtracting the one scattered radiation image from the medical image;
A medical image processing apparatus comprising:   The medical image processing apparatus according to claim 1, wherein the pixel value conversion unit converts a pixel value higher than the reference value to a pixel value lower than the reference value among the plurality of pixel values. The medical image processing apparatus according to claim 1, further comprising a reference value determination unit that determines the reference value based on a representative value of the plurality of pixel values. The medical image processing apparatus according to claim 3 , wherein the representative value is a mode value of the plurality of pixel values. The medical image processing apparatus according to claim 3, wherein the representative value is an average value or a median value of a plurality of pixel values included in a region of interest of the medical image. A subject thickness determining unit that determines a subject thickness based on X-ray conditions or projection data relating to the medical image;
A scattering function determining unit that determines the scattering function based on the X-ray condition and the object thickness;
The medical image processing apparatus according to any one of claims 1 to 5, characterized in. The scattered radiation image generator is
Transforming the Fourier transform of the transformed image into the scattered radiation image based on the Fourier transform of the scattering function;
The medical image processing apparatus according to any one of claims 1 to 6 . An X-ray diagnostic apparatus comprising the medical image processing apparatus according to any one of claims 1 to 7 ,
An X-ray generator for generating X-rays;
An X-ray detector for detecting the X-ray;
A medical image generator that generates the medical image based on an output from the X-ray detector;
An X-ray diagnostic apparatus further comprising: The reference value determining unit determines the reference value by multiplying the representative value by a predetermined constant;
The medical image processing apparatus according to claim 3 .

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