Source: https://patents.google.com/patent/JP6313168B2/en
Timestamp: 2019-12-13 21:03:14
Document Index: 778902700

Matched Legal Cases: ['art 14', 'art 38', 'art 381', 'art 382', 'art 383', 'art 384', 'art 384']

JP6313168B2 - X-ray CT apparatus, image processing apparatus, and image processing program - Google Patents
X-ray CT apparatus, image processing apparatus, and image processing program Download PDF
JP6313168B2
JP6313168B2 JP2014178450A JP2014178450A JP6313168B2 JP 6313168 B2 JP6313168 B2 JP 6313168B2 JP 2014178450 A JP2014178450 A JP 2014178450A JP 2014178450 A JP2014178450 A JP 2014178450A JP 6313168 B2 JP6313168 B2 JP 6313168B2
JP2014178450A
JP2016052349A (en
竹島　秀則
利幸 小野
井田　孝
2014-09-02 Application filed by キヤノンメディカルシステムズ株式会社 filed Critical キヤノンメディカルシステムズ株式会社
2014-09-02 Priority to JP2014178450A priority Critical patent/JP6313168B2/en
2016-04-14 Publication of JP2016052349A publication Critical patent/JP2016052349A/en
2018-04-18 Publication of JP6313168B2 publication Critical patent/JP6313168B2/en
Embodiments described herein relate generally to an X-ray CT apparatus, an image processing apparatus, and an image processing program.
As an application of X-ray CT (Computed Tomography), the type and atomic number of substances contained in a subject using projection data corresponding to multiple energy bands, utilizing the fact that X-ray absorption characteristics differ from substance to substance. There is a technique for discriminating density and the like. This is called substance discrimination. The higher the monochromaticity of the divided energy band, the greater the difference in interaction between a specific substance and other substances. For this reason, in order to perform substance discrimination with high accuracy, it is preferable to use X-rays with high monochromaticity, that is, X-rays with a narrow energy band.
On the other hand, if X-rays with a narrow energy band or low-dose X-rays are used to reduce the exposure dose of the subject, the number of photons in the X-rays decreases, making it more susceptible to noise. End up. For this reason, in the conventional substance discrimination method using multi-energy CT, it is difficult to perform substance discrimination processing with high accuracy when there is a lot of noise at a low dose.
JP-A-5-161633
The problem to be solved by the present invention is to provide an X-ray CT apparatus, an image processing apparatus, and an image processing program capable of performing material discrimination with higher accuracy.
The X-ray CT apparatus of the embodiment includes an X-ray tube, an X-ray detector, a derivation unit, a calculation unit, and a generation unit. The X-ray tube generates X-rays. The X-ray detector has a plurality of X-ray detection elements that output signals based on the incident X-rays. The deriving unit derives the constraint condition using at least one projection data among a plurality of projection data in which at least a part of the corresponding energy band is different. Using the projection data and the constraint conditions, the calculation unit calculates the total distance that the X-rays emitted from the X-ray tube and incident on the X-ray detection element have passed through the region where the substance to be distinguished exists. A certain effective distance is calculated. The generation unit generates image data for displaying information on the substance using the projection data and the effective distance.
FIG. 1 is a diagram showing an X-ray CT apparatus according to the first embodiment. FIG. 2 is a diagram showing a plurality of energy bands used in the first embodiment. FIG. 3 is a flowchart showing a procedure for substance discrimination performed by the X-ray CT apparatus according to the first embodiment. FIG. 4 is a flowchart showing the procedure performed in step S13 of FIG. FIG. 5 is a diagram illustrating a phantom in which the X-ray CT apparatus according to the first embodiment performs photon counting CT imaging. FIG. 6 is a diagram showing the first projection data. FIG. 7 is a view showing a CT image generated by reconstructing the first projection data. FIG. 8 is a diagram illustrating a first binarized image. FIG. 9 is a diagram showing first projection information derived from the first binarized image. FIG. 10 is a diagram showing a second binarized image. FIG. 11 is a diagram showing second projection information derived from the second binarized image. FIG. 12 is a diagram showing a selection screen used when selecting a constraint condition. FIG. 13 is a diagram showing a selection screen used when selecting a substance to be discriminated. FIG. 14 is a diagram showing a configuration of an X-ray CT apparatus according to the second embodiment. FIG. 15 is a flowchart showing a procedure for substance discrimination performed by the X-ray CT apparatus according to the second embodiment. FIG. 16 is a flowchart showing a procedure for generating image data of a substance to be distinguished by the X-ray CT apparatus according to the second embodiment. FIG. 17 is a diagram illustrating a phantom in which the X-ray CT apparatus according to the second embodiment performs dual energy CT imaging. FIG. 18 is a diagram illustrating a hardware configuration of an image processing apparatus according to an embodiment other than the first embodiment and the second embodiment.
Hereinafter, an embodiment of an X-ray CT apparatus will be described in detail with reference to the accompanying drawings. In the following embodiments, parts denoted by the same reference numerals perform the same operation, and redundant description will be omitted as appropriate.
FIG. 1 is a diagram showing an X-ray CT apparatus 1a according to the first embodiment. FIG. 2 is a diagram illustrating a plurality of energy bands used in the first embodiment. As shown in FIG. 1, the X-ray CT apparatus 1a includes a gantry device 10a, a couch device 20, and an image processing device 30a. The X-ray CT apparatus 1a according to the first embodiment is an apparatus capable of performing photon counting CT.
The gantry device 10a collects projection data, which will be described later, by irradiating the subject P with X-rays. The gantry device 10a includes a gantry controller 11a, an X-ray generator 12a, an X-ray detector 13a, a collection unit 14a, and a rotating frame 15.
The gantry controller 11a controls the operations of the X-ray generator 12a and the rotating frame 15 under the control of the scan controller 33 described later. The gantry control unit 11 a includes a high voltage generation unit 111 a, a collimator adjustment unit 112, and a gantry driving unit 113. The high voltage generator 111a supplies a tube voltage to an X-ray tube 121a described later. The collimator adjustment unit 112 adjusts the X-ray irradiation range irradiated to the subject P from the X-ray generator 12a by adjusting the opening degree and position of the collimator 123. For example, the collimator adjustment unit 112 adjusts the aperture of the collimator 123 to adjust the X-ray irradiation range, that is, the X-ray fan angle and cone angle. The gantry driving unit 113 rotates the rotary frame 15 to rotate the X-ray generator 12 a and the X-ray detector 13 a on a circular orbit around the subject P.
The X-ray generator 12a generates X-rays that irradiate the subject P. The X-ray generator 12a includes an X-ray tube 121a, a wedge 122, and a collimator 123. The X-ray tube 121a irradiates the subject with beam-shaped X-rays with the tube voltage supplied by the high voltage generator 111a. The X-ray tube 121a is a vacuum tube that generates beam-shaped X-rays having a conical shape and a pyramidal shape along the body axis direction of the subject P. This beam-shaped X-ray is also called a cone beam. The X-ray tube 121 a irradiates the subject P with a cone beam as the rotating frame 15 rotates. The wedge 122 is an X-ray filter for adjusting the X-ray dose of X-rays emitted from the X-ray tube 121a. The collimator 123 is a slit for narrowing the X-ray irradiation range in which the X-ray dose is adjusted by the wedge 122 under the control of the collimator adjustment unit 112.
The X-ray detector 13a is a multi-row detector having a plurality of X-ray detection elements that output signals based on incident X-rays in the channel direction and the slice direction. The channel direction is the circumferential direction of the rotating frame 15, and the slice direction is the body axis direction of the subject P. The X-ray detection element of the X-ray detector 13a outputs a pulsed electric signal that can measure the photon energy and count the number of photons every time one X-ray photon enters. The collection unit 14a described later can count the number of photons incident on the respective X-ray detection elements by counting the number of electrical signals. Moreover, the collection part 14a mentioned later can measure the energy of the photon which caused the output of the electric signal by performing the arithmetic processing based on the waveform of a pulse.
The X-ray detector 13a has, for example, a cadmium telluride (CdTe) semiconductor element, and the X-ray detector 13a is a so-called direct conversion type detector. A direct conversion type detector is a detector that directly converts photons incident on an X-ray detection element into an electrical signal. The electrical signal output from the X-ray detector 13a is such that electrons generated by the incidence of photons travel toward the positive potential collecting electrode and holes generated by the incidence of photons are applied to the negative potential collecting electrode. It is output at least one of traveling toward. The X-ray detector 13a shown in FIG. 1 may be a so-called indirect conversion type detector. An indirect conversion type detector is a detector that converts photons incident on an X-ray detection element into scintillator light by a scintillator and converts the scintillator light into an electrical signal by an optical sensor such as a photomultiplier tube.
The collection unit 14a collects count information that is a result of performing a count process using the electrical signal output from the X-ray detector 13a. The count information is information in which the position (view) of the X-ray tube 121a, the position of the X-ray detection element on which photons are incident, the photon energy, and the photon count value are associated with each other. Furthermore, the collection unit 14a collects projection data for each energy band having a predetermined width by allocating the energy of each photon measured from the electrical signal to a plurality of preset energy bands. The count value of photons included in the count information may be a value per unit time (count rate).
For example, the collection unit 14a classifies the collected count information for each photon energy at each position of each X-ray detection element and the X-ray tube 121a, and sets the photon count value to the first energy shown in FIG. The energy is distributed to any one of the band E1, the second energy band E2, the third energy band E3, the fourth energy band E4, the fifth energy band E5, and the sixth energy band E6. Thereby, the collection unit 14a obtains projection data corresponding to each of the first energy band E1, the second energy band E2, the third energy band E3, the fourth energy band E4, the fifth energy band E5, and the sixth energy band E6. Generate. Further, the collection unit 14a generates projection data obtained by adding the photon count values of at least two projection data among the plurality of projection data at each position of each X-ray detection element and the X-ray tube 121a. For example, the collection unit 14a collects six types of projection data having different energy bands for each view, and calculates the total number of photons of the six projection data at each position of the X-ray tube 121a and each X-ray detector. Projection data is generated by adding the numerical values. In the description of the first embodiment, the projection data obtained by adding the photon count values of the projection data of a plurality of energy bands at each position of the X-ray tube 121a and each X-ray detection element is defined as the first projection data. Each of the projection data before summing the photon count values of the projection data of a plurality of energy bands is defined as second projection data. Since the first projection data is the sum of the photon count values of these six second projection data at each position of each X-ray detection element and X-ray tube 121a, the number of X-ray photons is large. There is little noise. That is, the energy band corresponding to the first projection data is different from the energy band used for the substance discrimination process. The first projection data uses the projection data of all energy bands shown in FIG. The first projection data may be projection data obtained by adding the photon count values of two or more and five or less second projection data as long as the influence of noise can be reduced. For example, the first projection data is a projection obtained by adding the photon count values of the second projection data in the first energy band E1, the second energy band E2, the third energy band E3, and the fourth energy band E4 shown in FIG. It can be data.
In FIG. 2, the first energy band E1, the second energy band E2, the third energy band E3, and the fourth energy having the same energy width on the energy distribution of the X-rays irradiated to the subject P from the X-ray tube 121a. An example in which a band E4, a fifth energy band E5, and a sixth energy band E6 are set is shown. As shown in FIG. 2, in the first embodiment, a calculation unit 383 (described later) is effective in a range in which all energy bands corresponding to projection data used when a derivation unit 381 a (described later) derives a constraint condition are combined. It is wider than the combined range of all energy bands corresponding to the projection data used when calculating the distance.
Note that the method of setting the energy band on the energy distribution of the X-rays irradiated to the subject P is not limited to that shown in FIG. The number of energy bands, the width of energy bands, and the like can be arbitrarily set. A plurality of energy bands may partially overlap. In addition, setting energy bands on both sides of the substance to be discriminated across the K absorption edge is preferable in performing substance discrimination because the value of the linear attenuation coefficient differs greatly on both sides of the K absorption edge. Furthermore, if an energy band is set so that contrast can be easily obtained according to the substance to be discriminated, substance discrimination can be performed with higher accuracy. For example, hard tissue such as bone is more easily transmitted by high-energy X-rays than low-energy X-rays. Therefore, when the energy in the energy band is set high, contrast is easily obtained. On the other hand, since soft tissue such as cartilage is easier to transmit X-rays having lower energy than X-rays having higher energy, contrast is easily obtained when the energy in the energy band is set low. The X-ray CT apparatus 1a according to the first embodiment is configured such that settings of a plurality of energy bands can be arbitrarily changed by an operator, for example. Further, for example, the control unit 38a described later controls the distribution of the photon count values performed by the collection unit 14a by notifying the gantry device 10a of the energy band setting information. In the first embodiment, the generation of the first projection data may be performed by the image processing device 30a.
The collection unit 14a transmits the collected projection data to the image processing device 30a. For example, the collection unit 14a transmits projection data of each view in a sinogram data format. The sinogram is data in which signals detected by the X-ray detector 13a at each position (each view) of the X-ray tube 121a are arranged. The sinogram detects an X-ray in a two-dimensional orthogonal coordinate system in which the first direction is a view direction which is the position of the X-ray tube 121a and the second direction orthogonal to the first direction is a channel direction of the X-ray detector 13a. This is data to which a signal (in this embodiment, a count value) detected by the device 13a is assigned. The collection unit 14a generates a sinogram in units of columns in the slice direction. In the following description, a case where the projection data is a sinogram will be described as an example. The collection unit 14a is also called a DAS (Data Acquisition System).
The rotating frame 15 is an annular frame that supports the X-ray generator 12a and the X-ray detector 13a so as to face each other with the subject P interposed therebetween. The rotating frame 15 is driven by the gantry driving unit 113 and rotates at a high speed on a circular orbit around the subject P.
The couch device 20 includes a couch driving device 21 and a top plate 22 on which the subject P is placed. The couch driving device 21 moves the subject P within the rotating frame 15 by moving the top plate 22 on which the subject P is placed in the Z-axis direction under the control of the scan control unit 33 described later. . Note that the gantry device 10a performs, for example, a helical scan that rotates the rotating frame 15 while moving the top plate 22 to scan the subject P in a spiral shape. Alternatively, the gantry device 10a performs a conventional scan in which the subject P is scanned in a circular orbit by rotating the rotating frame 15 while the position of the subject P is fixed after the top plate 22 is moved. Alternatively, the gantry device 10a executes a step-and-shoot method in which a conventional scan is performed in a plurality of scan areas by moving the position of the top plate 22 at regular intervals.
The image processing apparatus 30a accepts the operation of the X-ray CT apparatus 1a by the operator and performs various image processes such as a CT image reconstruction process using the projection data collected by the gantry apparatus 10a. The image processing apparatus 30a includes an input unit 31, a display unit 32, a scan control unit 33, a preprocessing unit 34, a data storage unit 35, an image reconstruction unit 36, an image storage unit 37, and a control unit 38a. With.
The input unit 31 is a mouse, a keyboard, or the like used by the operator of the X-ray CT apparatus 1a to input various instructions and various settings, and transfers instructions and setting information received from the operator to the control unit 38a. The display unit 32 is a monitor that is referred to by the operator. The display unit 32 displays a CT image, a display image to be described later, a GUI (Graphical User Interface) for receiving various settings from the operator via the input unit 31, and the like. The input unit 31 is used to select a constraint condition described later.
The scan control unit 33 controls operations of the gantry control unit 11a, the collection unit 14a, and the bed driving device 21 under the control of the control unit 38a. Specifically, the scan control unit 33 controls the gantry control unit 11a to rotate the rotating frame 15 and irradiate the X-ray tube 121a with X-rays when performing photon counting CT imaging. The opening degree and position of 123 are adjusted. The scan control unit 33 controls the collection unit 14a under the control of the control unit 38a. Further, the scan control unit 33 moves the top 22 by controlling the bed driving device 21 during imaging of the subject P under the control of the control unit 38a.
The preprocessing unit 34 performs correction processing such as logarithmic conversion, offset correction, sensitivity correction, beam hardening correction, and scattered radiation correction on the projection data generated by the collection unit 14 a, and stores this in the data storage unit 35. Store. The projection data that has been subjected to the correction process by the preprocessing unit 34 is also referred to as raw data.
The data storage unit 35 stores raw data, that is, projection data that has been corrected by the preprocessing unit 34. Hereinafter, in order to simplify the explanation, the raw data may be described as projection data.
The image reconstruction unit 36 reconstructs the projection data stored in the data storage unit 35 and generates a CT image. As the reconstruction method, there are various methods, for example, back projection processing. In addition, as the back projection processing, for example, an FBP (Filtered Back Projection) method can be cited. Note that the image reconstruction unit 36 may perform reconstruction processing by, for example, a successive approximation method. The image reconstruction unit 36 stores the generated CT image in the image storage unit 37.
The image storage unit 37 stores a CT image reconstructed by the image reconstruction unit 36 and a display image described later. For example, in the first embodiment, the image reconstruction unit 36 generates a CT image using the projection data stored in the data storage unit 35 as the first projection data, and stores the CT image in the image storage unit 37. .
The control unit 38a controls the X-ray CT apparatus 1a by controlling the operations of the gantry device 10a, the couch device 20, and the image processing device 30a. The control unit 38a controls the scan control unit 33 to execute scanning, and collects projection data from the gantry device 10a. The control unit 38a controls the preprocessing unit 34 to perform the above-described correction processing on the projection data. The control unit 38a controls the display unit 32 to display the projection data stored in the data storage unit 35 and the image data stored in the image storage unit 37.
The data storage unit 35 and the image storage unit 37 described above can be realized by a RAM (Random Access Memory), a semiconductor memory element such as a flash memory, a hard disk, an optical disk, or the like. Further, the scan control unit 33, the preprocessing unit 34, the image reconstruction unit 36, and the control unit 38a described above may be an integrated circuit such as an application specific integrated circuit (ASIC) or a field programmable gate array (FPGA) or a central processing unit (CPU). ), And an electronic circuit such as an MPU (Micro Processing Unit).
And the control part 38a which concerns on 1st Embodiment is provided with the derivation | leading-out part 381a, the calculation formula derivation | leading-out part 382a, the calculation part 383, and the production | generation part 384, as shown in FIG.
The deriving unit 381a derives the constraint condition using at least one projection data among a plurality of projection data in which at least a part of the corresponding energy band is different. Specifically, the derivation unit 381a generates a binarized image from the CT image obtained by reconstructing the projection data by binarization using a threshold value set according to the substance to be discriminated, and the binarized image is obtained. A constraint condition is derived using the projection information obtained by the projection processing. Further, the deriving unit 381a generates a plurality of binarized images from the CT image obtained by reconstructing the projection data by binarization using a plurality of threshold values set according to the substance to be discriminated, and a plurality of binaries A plurality of constraint conditions may be derived using a plurality of pieces of projection information obtained by projecting the digitized image. The calculation formula deriving unit 382a derives a calculation formula for calculating the effective distance of the substance to be distinguished from the second projection data. Here, the effective distance of the substance to be discriminated is the substance that is discriminated by the X-rays emitted from the X-ray tube 121a, transmitted through the subject P, and incident on the X-ray detection element of the X-ray detector 13a. This is the total distance transmitted through the existing area. The calculation unit 383 calculates the effective distance of the substance to be discriminated using the projection data and the constraint conditions. The generation unit 384 generates image data for displaying information on the substance using the projection data and the effective distance.
Hereinafter, an example of processing performed by the deriving unit 381a, the calculation formula deriving unit 382a, the calculating unit 383, and the generating unit 384 will be described in detail with reference to FIGS. FIG. 3 is a flowchart showing a procedure for substance discrimination performed by the X-ray CT apparatus 1a according to the first embodiment. FIG. 4 is a flowchart showing the procedure performed in step S13 of FIG. FIG. 5 is a diagram illustrating a phantom PHa in which the X-ray CT apparatus 1a according to the first embodiment performs photon counting CT imaging. FIG. 6 is a diagram showing the first projection data P1. FIG. 7 is a diagram showing a CT image im generated by reconstructing the first projection data P1. FIG. 8 is a diagram illustrating the first binarized image B1. FIG. 9 is a diagram showing the first projection information PJ1 derived from the first binarized image B1. FIG. 10 is a diagram illustrating the second binarized image B2. FIG. 11 is a diagram showing the second projection information PJ2 derived from the second binarized image B2.
In the following description, a case where photon counting CT imaging is performed using the phantom PHa shown in FIG. The phantom PHa includes a cylinder C1a, a cylinder C2a, a cylinder C3a, and a cylinder C4a whose central axes are parallel to each other and whose bottom diameters are different from each other. The diameter of the cylinder C1a is larger than the diameters of the cylinder C2a, the cylinder C3a, and the cylinder C4a. The cylinder C2a, the cylinder C3a, and the cylinder C4a are included in the cylinder C1a. The inside of the cylinder C2a is filled with air A. The inside of the cylinder C3a is filled with the gadolinium contrast agent G. The inside of the cylinder C4a is filled with the iodine contrast medium I. The area surrounded by the cylinder C2a, the cylinder C3a, the cylinder C4a, and the cylinder C1a is filled with water W. The phantom PHa is disposed in the air.
The control unit 38a controls the gantry device 10a, the couch device 20, and the image processing device 30a to execute photon counting CT imaging, collects projection data, and controls the preprocessing unit 34 to correct the projection data as described above. (Step S11). In step S11, correction processing is performed on the first projection data and the second projection data of each of the plurality of energy bands. FIG. 6 shows a sinogram of the first projection data P1, which is projection data having all information of a plurality of energy bands. In FIG. 6, the vertical direction is the view direction, and the horizontal direction is the channel direction.
As shown in FIG. 6, the first projection data P1 includes a region Mp, a region Ap, a region Ip, a region Gp, and a region Wp. The region Mp is a rectangular region that is long in the view direction and is located at both ends of the first projection data P1 in the channel direction. The region Ap, the region Ip, and the region Gp are band-like regions that meander along the view direction. The region Wp is a region other than the region Ap, the region Ip, the region Gp, and the region Mp on the first projection data P1. Each point in the region Mp includes information on the count value of X-ray photons that have passed through the air without passing through the phantom PHa. Each point in the region Ap includes at least information on the count value of photons of X-rays that have passed through the air A in the cylinder C2a. Each point in the region Ip includes at least information on the count value of photons of X-rays that have passed through the iodine contrast medium I. Each point in the region Gp includes at least information on the count value of photons of X-rays that have passed through the gadolinium contrast agent G. Each point in the region Wp includes information on the count value of X-ray photons that have passed through only the water W.
The image reconstruction unit 36 reconstructs the first projection data P1 stored in the data storage unit 35 and generates the CT image im shown in FIG. 7 (step S12). As shown in FIG. 7, the CT image im shows a region Wi corresponding to water W, a region Ai corresponding to air A, a region Ii corresponding to iodine contrast agent I, and a region Gi corresponding to gadolinium contrast agent G. It is. The control unit 38a performs various processes on the CT image im generated in step S12, and generates image data of a substance to be distinguished (step S13). The display unit 32 displays the CT image im and the display image (step S14). Here, the display image refers to an image that displays information on a substance to be discriminated. Examples of information regarding the substance to be distinguished include type, atomic number, density, and the like. Details of step S13 are as described below.
The deriving unit 381a binarizes the CT image im and generates the first binarized image B1 shown in FIG. 8 (step S101). The first binarized image B1 is an image obtained by dividing the CT image im into a region A1 where the air A exists and a region O1 where the air A does not exist. A region A1 on the first binarized image B1 corresponds to a region Ai on the CT image im. The region O1 on the first binarized image B1 corresponds to a region obtained by combining the region Wi, the region Ii, and the region Gi on the CT image im. Since the linear attenuation coefficient of air A is smaller than the linear attenuation coefficient of other substances, in the CT image im, the luminance of the area Ai where the air A exists and the areas other than the air A (area Wi, area Ii and area) The difference from the brightness of Gi) becomes large. For this reason, the deriving unit 381a performs binarization using a threshold value set according to the air, and the CT image im is a high-luminance region in which the luminance value of a pixel whose luminance value is equal to or greater than the threshold value is 1, that is, the region It can be easily divided into A1 and a low luminance region where the luminance value of a pixel whose luminance value is smaller than the threshold is 0, that is, the region O1. Therefore, the deriving unit 381a can easily generate the first binarized image B1 from the CT image im.
The deriving unit 381a derives the first projection information PJ1 shown in FIG. 9 from the first binarized image B1 (step S102). The deriving unit 381a geometrically arranges and projects the first binarized image B1 divided into an air region and a region other than air with the X-ray tube 121a and the X-ray detector 13a ( The first projection information PJ1, which is projection information, is derived by calculating an average value projection image of the region division result by projection processing based on information on the (view direction). The 1st projection information PJ1 becomes information which can acquire transmission total distance of fields other than air. For example, as shown in FIG. 9, the deriving unit 381a derives the first projection information PJ1 in the sinogram data format in the same manner as the first projection data P1.
The luminance of each point in the first projection information PJ1 includes information on the total transmission distance. The total transmission distance is a distance through which X-rays emitted from the X-ray tube 121a, transmitted through the subject P, and incident on the X-ray detection element of the X-ray detector 13a have passed through a region where no air A exists. Total. As shown in FIG. 9, the first projection information PJ1 includes a region Mp1, a region Ap1, and a region Op1. The region Mp1 is a rectangular region that is long in the view direction and is located at both ends of the first projection information PJ1 in the channel direction. The region Ap1 is a belt-like region that meanders along the view direction. The region Op1 is a region other than the region Mp1 and the region Ap1 on the first projection information PJ1.
The luminance of each point in the region Ap1 includes at least information on the total transmission distance of X-rays that have passed through the air A in the cylinder C2a. The luminance of each point in the region Op1 includes information on the total transmission distance of X-rays that are not transmitted through the air A in the cylinder C2a.
However, the luminance of each point of the first projection information PJ1 includes the total distance that the X-rays have passed through the water W, the total distance that the X-rays have passed through the iodine contrast agent I, and the X-rays that have passed through the gadolinium contrast agent G. It does not contain information about the total distances made. This is because the first projection information PJ1 does not distinguish the region Wi where the water W exists, the region Ii where the iodine contrast agent I exists, and the region Gi where the gadolinium contrast agent exists in the CT image im. This is because 1 is generated from the binarized image B1. The total transmission distance is used for the first constraint condition described later.
The deriving unit 381a binarizes the CT image im and generates the second binarized image B2 shown in FIG. 10 (step S103). The second binarized image B2 is an image obtained by dividing the CT image im into a region obtained by combining the region I2 in which the iodinated contrast agent I exists and the region G2 in which the gadolinium contrast agent G is present, and the other region O2. is there. A region I2 on the second binarized image B2 corresponds to a region Ii on the CT image im. A region G2 on the second binarized image B2 corresponds to a region Gi on the CT image im. A region O2 on the second binarized image B2 corresponds to a region obtained by combining the region Ai and the region Wi on the CT image im. Since the linear attenuation coefficient of the iodine contrast agent I and the gadolinium contrast agent G is larger than the linear attenuation coefficient of the water W and the air A, the region Ii where the iodine contrast agent I exists and the gadolinium contrast agent G are present in the CT image im. The difference between the luminance of the region combined with the existing region Gi and the luminance of the other regions, that is, the region combined with the region Wi where the water W exists and the region Ai where the air A exists increases. For this reason, the deriving unit 381a converts the CT image im into a high-luminance region having a luminance value of 1, that is, the region I2 and the region G2, and the luminance by binarization using a threshold value set according to the substance to be distinguished. It can be easily divided into a low luminance region having a value of 0, that is, the region O2. Therefore, the deriving unit 381a can easily generate the second binarized image B2 from the CT image im.
The deriving unit 381a derives the second projection information PJ2 shown in FIG. 11 from the second binarized image B2 (step S104). The second projection information PJ2 is acquired by a projection process similar to the process performed when obtaining the first projection data PJ1. For example, as shown in FIG. 11, the deriving unit 381a derives the second projection information PJ2 in the sinogram data format.
The luminance of each point of the second projection information PJ2 includes information on the effective distance of the iodine contrast agent I and the effective distance of the gadolinium contrast agent G. As shown in FIG. 11, the second projection information PJ2 includes a region Mp2, a region Ip2, a region Gp2, and a region Op2. The region Mp2 is a rectangular region that is long in the view direction and is located at both ends of the second projection information PJ2 in the channel direction. The region Ip2 and the region Gp2 are band-like regions that meander along the view direction. The region Mp2 is a region other than the region Mp2, the region Ip2, and the region Gp2 on the second projection information PJ2.
The luminance of each point in the region Ip2 includes information on at least one of the effective distance of the X-ray iodine contrast agent I and the effective distance of the gadolinium contrast agent G transmitted through the iodine contrast agent I. The luminance of each point in the region Gp2 includes information on at least one of the effective distance of the X-ray iodine contrast agent I and the effective distance of the gadolinium contrast agent G transmitted through the gadolinium contrast agent G. The brightness of each point in the region Op2 includes information on the effective distance of the iodine contrast agent I and the effective distance of the gadolinium contrast agent G of the X-ray that does not pass through the iodine contrast agent I and the gadolinium contrast agent G. . However, the information obtained from the second projection information PJ2 is information on the total distance of the effective distance of the iodinated contrast agent I and the effective distance of the gadolinium contrast agent G, and the effective distance of the iodized contrast agent I and the gadolinium contrast The effective distance of the agent G cannot be obtained individually. Note that the luminance value at each point of the second projection data PJ2 represents the existence probability of the iodine contrast agent I and the gadolinium contrast agent G. The existence probability is used for a second constraint condition described later.
Further, the brightness of each point of the second projection information PJ2 does not include information on the effective distance of the air A and the effective distance of the water W. This is because the second projection information PJ2 is generated from the second binarized image B2 that does not distinguish the region Wi where the water W exists and the region Ai where the air A exists in the CT image im. Because there is.
The derivation unit 381a may display the first binarized image B1 and the second binarized image B2 on the display unit 32 in the vicinity of the corresponding display image. The display image is an image that displays the result of substance discrimination, and is generated based on image data of the substance to be discriminated. Thereby, the operator of the X-ray CT apparatus 1a or the X-ray CT apparatus 1b can confirm the method by which the effective distance of the distinguished substance is calculated, and appropriately change the method for calculating the effective distance as necessary. it can.
The derivation unit 381a displays the first projection information PJ1 and the second projection information PJ2 on the display unit 32, and the operator uses either the first projection information PJ1 or the second projection information PJ2 when performing material discrimination. You may make it select whether to do. Alternatively, the first projection information PJ1 or the second projection information PJ2 may be automatically selected based on the electronic medical record and the imaging conditions. Thereby, substance discrimination can be performed according to the operator's needs, diagnosis results, imaging conditions, and the like.
Further, the operator corrects the first binarized image B1 and the second binarized image B2 via the input unit 31, and the derivation unit 381a generates first projection information and second projection information again, which will be described later. Material discrimination may be performed. Thereby, the substance discrimination according to the operator's needs can be performed.
The calculation formula deriving unit 382a derives a calculation formula for calculating the effective distance of the substance to be discriminated (step S105). First, a method for calculating an effective distance of a substance to be discriminated by the conventional technique will be described. In general, the number of photons of X-rays irradiated to the subject P is C 0 , the number of photons of X-rays detected by the X-ray detection element is C, the energy of X-rays is E, and the X-rays in the nth energy band If the energy of (n = 1, 2,..., 6) is defined as E n , the number of substances to be distinguished is m, the linear attenuation coefficient of the substances to be distinguished is μ j , and the effective distance of the substances to be distinguished is defined as L j , Equation (1) is established. In the related art, the second energy band E1, the second energy band E2, the third energy band E3, the fourth energy band E4, the fifth energy band E5, and the second energy band E6 shown in FIG. Formula (2), which is a simultaneous equation using projection data, is established to calculate the effective distance of the substance to be discriminated.
Note that since the subject P in the first embodiment is the phantom PHa, the substances to be discriminated, that is, the substances for calculating the density distribution are the water W, the iodine contrast medium I, and the gadolinium contrast medium G. Therefore, in the first embodiment, “m = 3”. In the subscript j in the formula (1), “j = 1” represents the iodine contrast medium I, “j = 2” represents the gadolinium contrast medium G, and “j = 3” represents the water W.
In the conventional substance discrimination, the effective distance of the substance to be discriminated is calculated using the above-described equation (2), and image data of the substance to be discriminated is generated. However, the left side of Equation (2) has a large energy band and a small number of photons, so it is highly influenced by noise, and it is difficult to accurately calculate the effective distance of the substance to be distinguished from Equation (2) alone. there were. Therefore, in the present invention, Equation (2) is solved under the constraint conditions described later, the effective distance of the substance is accurately calculated, and the substance discrimination is performed with higher accuracy.
The deriving unit 382a derives a constraint condition (Step S106). In the first embodiment, the constraint condition includes a first constraint condition and a second constraint condition described below.
The deriving unit 382a derives the first constraint condition. Specifically, the deriving unit 382a calculates the total transmission distance d at each point of the projection data used for calculating the effective distance from the CT image im obtained by reconstructing the projection data used for deriving the constraint condition. To do. For example, the deriving unit 382a calculates the total transmission distance d from information included in one point of the first projection information PJ1, sets the following formula (3), and combines this with the formula (2) to formula (4) Is derived. Equation (3) is the first constraint condition. Equation (3) is also called a regularization term. The first binarized image B1 is an image obtained by dividing the CT image im into a region A1 where the air A exists and a region O1 where the air A does not exist. For this reason, the deriving unit 382a can calculate the total transmission distance. Equation (3) is the length of X-rays emitted from the X-ray tube 121a and incident on one of the X-ray detection elements included in the X-ray detector 13a, that is, the length of the iodine that has passed through the region O1 where no air A exists. effective distance L 1 of the contrast agent I, which represents the sum of the effective distance L 3 of the effective distance L 2 and the water W of gadolinium contrast agent G, the first constraint that is a transmission total distance d equal.
The deriving unit 382a derives the second constraint condition. Specifically, the deriving unit 382a has the existence probability of the substance to be distinguished at each point of the projection data used for calculating the effective distance from the CT image im obtained by reconstructing the projection data used for deriving the constraint condition. d is calculated. For example, the deriving unit 382a calculates the existence probability p of the iodine contrast agent I or the gadolinium contrast agent G from the luminance of one point of the second projection information PJ2, and derives the following equation (5). Equation (5) is the second constraint condition. The second binarized image B2 is an image obtained by dividing the CT image im into a region where the region I2 where the iodinated contrast agent I is present and the region G2 where the gadolinium contrast agent G is present and the other region O2. . Therefore, derivation unit 382a can not be calculated effective distance L 2 of the effective distance L 1 and gadolinium contrast agent G of iodinated contrast agents I. However, derivation unit 382a may be set based on the minimum and maximum values of the sum of the effective distance L 2 of the effective distance L 1 and gadolinium contrast agent G of iodinated contrast I in the presence probability p. For this reason, the second constraint is an inequality as shown in Expression (5). In the equation (5), α and β are correction coefficients. The coefficient α and the coefficient β may be determined empirically or theoretically.
The calculating unit 383 calculates the effective distance of the substance to be discriminated (step S107). Specifically, the calculation unit 383 calculates the effective distance using the projection data obtained by adding the constraint condition and the photon count value at each point of the at least two projection data. More specifically, the calculation unit 383 calculates the effective distance L 1 of the iodinated contrast agent I and the gadolinium contrast from the equation (4) derived including the first constraint and the equation (5) as the second constraint. calculating the effective distance effective distance L 3 of the effective distance L 2 and the water W of agents G. Next, the calculation unit 383 determines whether or not the processing in steps S105 to S107 has been performed on all points on the first projection data P1 (step S108). When the processes of steps S105 to S107 are not performed at all points on the first projection data P1 (No at step S108), the process returns to step S105. If the processes in steps S105 to S107 have been performed at all points on the first projection data P1 (Yes in step S108), the process proceeds to step S109.
The generation unit 384 reconstructs the effective distance of the substance to be discriminated and calculates information regarding the substance to be discriminated (step S109). Specifically, the calculation unit 383, the effective distance L 1 iodinated contrast agent I, reconfigure the effective distance L 3 of the effective distance L 2 and the water W of gadolinium contrast agent G, the density distribution of the iodine contrast agent I, The density distribution of the gadolinium contrast agent G and the density distribution of the water W are calculated.
The generation unit 384 generates image data of the substance to be discriminated (step S110). For example, the generation unit 384 generates image data for displaying information related to the substance to be discriminated based on the projection data used for calculating the effective distance and the transmission total distance d. Or the production | generation part 384 produces | generates the image data for displaying the information regarding the substance to discriminate | determine based on the projection data used for calculation of effective distance, and the existence probability p. Specifically, the generation unit 384 generates image data that is data for displaying the density distribution of the iodine contrast agent I, the density distribution of the gadolinium contrast agent G, and the density distribution of the water W in the CT image im. The image data is output to the display unit 32, and the display unit 32 displays the CT image im, the display image of the iodine contrast agent I, the display image of the gadolinium contrast agent G, and the display image of the water W superimposed on the CT image im. For example, the generation unit 384 may assign colors to the display image of the iodine contrast agent I, the display image of the gadolinium contrast agent G, and the display image of the water W, respectively. Thereby, the operator can easily identify the discriminated substance.
The example of the process of the X-ray CT apparatus 1a according to the first embodiment has been described above. As described above, the X-ray CT apparatus 1a uses the calculation formula derived from the second projection data under the constraint condition calculated from the first projection data P1, that is, the first constraint condition and the second constraint condition. effective distance L 1 of the contrast agent I, calculates the effective distance L 3 of the effective distance L 2 and the water W of gadolinium contrast agent G. The effective distances L 1 , L 2 and L 3 calculated by the X-ray CT apparatus 1a are the sum of the photon count values of these six second projection data at the respective positions of the X-ray detection elements and the X-ray tube 121a. Therefore, the calculation is performed under the first constraint condition and the second constraint condition calculated from the first projection data P1 having a large number of X-ray photons and a small influence of noise. For this reason, the X-ray CT apparatus 1a according to the first embodiment can suppress a decrease in the accuracy of substance discrimination due to noise. Further, it is preferable that the constraint condition is derived from projection data in which the influence of noise is not maximum. As a result, the X-ray CT apparatus 1a according to the first embodiment calculates the effective distance of the substance to be discriminated under the constraint condition derived from the projection data in which the influence of noise is not the maximum. It can suppress that the precision of substance discrimination falls by projection data which is.
In addition, the X-ray CT apparatus 1a according to the first embodiment does not perform reconstruction of the first projection data P1, but under the first constraint condition and the second constraint condition calculated from the first projection data P1. The effective distances L 1 , L 2, and L 3 may be calculated using a calculation formula derived from the second projection data. The X-ray CT apparatus 1a reconstructs the first projection data P1, and then derives from the second projection data under the first constraint condition or the second constraint condition calculated from the first projection data P1. The effective distances L 1 , L 2, and L 3 may be calculated using the calculated formula. Further, the X-ray CT apparatus 1a does not reconstruct the first projection data P1, but derives it from the second projection data under the first constraint condition and the second constraint condition calculated from the first projection data P1. The effective distances L 1 , L 2, and L 3 may be calculated using a calculation formula. Note that a range in which all energy bands corresponding to the second projection data are combined may be set based on a constraint condition.
Further, the second projection data may be projection data obtained by adding the count values of photons in a plurality of energy bands at each position of the X-ray tube 121a and each X-ray detection element. For example, the second projection data includes the photon count values in two to five energy bands of the six energy bands shown in FIG. 2 at each position of the X-ray tube 121a and each X-ray detection element. Projection data obtained by summing may be used. Furthermore, in the above-described example, the energy band corresponding to the second projection data partially overlaps the energy band corresponding to the first projection data, but the energy band corresponding to the first projection data and the second projection The energy band corresponding to the data may not overlap at all.
In addition, it is not necessary to perform reconstruction on an area where there is no substance to be discriminated on the first projection data P1 or an area where the existence probability of the substance to be discriminated is low. For example, it is not necessary to perform reconstruction in a region where there is no iodine contrast agent I or gadolinium contrast agent G and a region where the existence probability of the iodine contrast agent I or gadolinium contrast agent G is low. Thereby, since only the part which needs to be reconfigure | reconstructed should be reconfigure | reconstructed, a processing load is reduced and the result of a substance discrimination can be displayed rapidly.
Next, a selection screen presented to the operator at the time of substance discrimination will be described with reference to FIGS. FIG. 12 is a diagram showing a selection screen presented when selecting a constraint condition. FIG. 13 is a diagram showing a selection screen presented when selecting a substance to be discriminated.
The display unit 32 displays the selection screen as shown in FIG. 12 so that the operator of the X-ray CT apparatus 1a can select the constraint condition used when calculating the effective distance of the substance to be discriminated. Good. The selection screen shown in FIG. 12 is a radio button RB1 for selecting only the transmission total distance d as a constraint condition, and a radio for selecting only the existence probability p of the iodinated contrast agent I or the gadolinium contrast agent G as a constraint condition. The button RB2, and the radio button RB3 for selecting the transmission total distance d and the existence probability p of the iodinated contrast medium I or the gadolinium contrast medium G as constraints. Thus, the operator can select the radio button RB1, the radio button RB2, or the radio button RB3 included in the selection screen and select a preferable constraint condition for calculating the effective distance of the substance to be discriminated.
The display unit 32 may display a selection screen as shown in FIG. 13 so that the operator of the X-ray CT apparatus 1a can select a substance to be displayed. The selection screen shown in FIG. 13 has a check box CK1 for displaying information about water W on the display unit 32, a check box CK2 for displaying information about iodine contrast medium I on the display unit 32, and the display unit 32. A check box CK3 for displaying information related to the gadolinium contrast agent G is provided. Accordingly, the operator can select at least one of the check box CK1, the check box CK2, and the check box CK3 included in the selection screen, and can display only the substance necessary for diagnosis on the display unit 32.
In the first embodiment, a case has been described in which material discrimination using constraint conditions is performed in the X-ray CT apparatus 1a that performs photon counting CT. However, the substance discrimination using the constraint conditions described in the first embodiment is performed by imaging with a plurality of different tube voltages, and using a normal integral X-ray detector, projection data of a plurality of energy bands. It is also applicable to a device that collects Therefore, in the second embodiment, a case where the image processing method described in the first embodiment is applied to a dual energy CT apparatus that collects projection data of a plurality of energies using two different tube voltages will be described. To do.
FIG. 14 is a diagram showing an X-ray CT apparatus 1b according to the second embodiment. As shown in FIG. 14, the X-ray CT apparatus 1b includes a gantry device 10b, a couch device 20, and an image processing device 30b.
The gantry device 10b collects projection data by irradiating the subject P with X-rays. The gantry device 10b includes a gantry controller 11b, an X-ray generator 12b, an X-ray detector 13b, a collecting unit 14b, and a rotating frame 15.
The gantry control unit 11 b controls the operations of the X-ray generator 12 b and the rotating frame 15 under the control of the scan control unit 33. The gantry control unit 11b includes a high voltage generation unit 111b, a collimator adjustment unit 112, and a gantry driving unit 113. The high voltage generator 111b supplies a plurality of tube voltages having different values to the X-ray tube 121b. For example, the high voltage generator 111b supplies two tube voltages having different values to the X-ray tube 121b. Thereby, the X-ray tube 121b generates two types of X-rays having different energy distributions. For this reason, the projection data collected by the collection unit 14b includes first projection data and second projection data. The tube voltage supplied to the X-ray tube 121b differs between the first projection data and the second projection data.
When the high voltage generator 111b supplies three or more tube voltages having different values to the X-ray tube 121b, the X-ray tube 121b has three or more types of X-rays having different energy distributions to the subject P. May be irradiated.
The X-ray detector 13b is a multi-row detector having a plurality of X-ray detection elements that output signals based on incident X-rays in the channel direction and the slice direction. The X-ray detection element of the X-ray detector 13b generates the X-ray tube 121b and detects the intensity of the X-ray irradiated to the subject P. The collection unit 14b collects a plurality of projection data by collecting the intensity of a plurality of X-rays having different energy distributions generated by a plurality of tube voltages. For example, the collection unit 14b collects X-ray projection data generated by the first tube voltage (140 kV) as first projection data, and the X-ray projection data generated by the second tube voltage (80 kV). , Collected as second projection data. The high voltage generator 111b supplies three or more types of tube voltages having different values to the X-ray tube 121b, and the subject P is irradiated with three or more types of X-rays having different energy distributions. In this case, the collection unit 14b collects the same number of projection data as the number of types of tube voltages to be applied.
The image processing device 30b includes an input unit 31, a display unit 32, a scan control unit 33, a preprocessing unit 34, a data storage unit 35, an image reconstruction unit 36, an image storage unit 37, and a control unit 38b. With.
The control unit 38b controls the X-ray CT apparatus 1b by controlling the operations of the gantry device 10b, the couch device 20, and the image processing device 30b. As illustrated in FIG. 14, the control unit 38b includes a derivation unit 381a, a calculation formula derivation unit 382b, a calculation unit 383, and a generation unit 384.
The derivation unit 381b derives the constraint condition using at least two projection data among the plurality of projection data collected by the collection unit 14b. That is, in the second embodiment, the deriving unit 381b derives the constraint condition using the first projection data and the second projection data. The calculation formula deriving unit 382b derives a calculation formula for calculating the effective distance of the substance to be distinguished from the first projection data and the second projection data. Details of the deriving unit 381b and the calculation formula deriving unit 382b will be described later.
Next, an example of processing of the X-ray CT apparatus 1b according to the second embodiment will be described with reference to FIGS. FIG. 15 is a flowchart showing a procedure for substance discrimination performed by the X-ray CT apparatus 1b according to the second embodiment. FIG. 16 is a flowchart illustrating a procedure for generating image data of a substance to be distinguished by the X-ray CT apparatus 1b according to the second embodiment. FIG. 17 is a diagram illustrating a phantom PHb in which the X-ray CT apparatus 1b according to the second embodiment performs dual energy CT imaging.
In the following description, a case where dual energy CT imaging is performed using the phantom PHa described in the first embodiment as the subject P will be described as an example. A case where dual energy CT imaging is performed with the phantom PHb shown in FIG. 17 as the subject P will be described as an example. The phantom PHb includes a cylinder C1b, a cylinder C2b, and a cylinder C4b whose central axes are parallel to each other and whose bottom diameters are different from each other. The diameter of the cylinder C1b is larger than the diameters of the cylinder C2b and the cylinder C4b. The cylinder C2b and the cylinder C4b are included in the cylinder C1b. The inside of the cylinder C2b is filled with air A. The inside of the cylinder C4b is filled with the iodine contrast medium I. The area surrounded by the cylinder C2b and the cylinder C4b and the cylinder C1b is filled with water W. The phantom PHb is disposed in the air.
The control unit 38b controls the gantry device 10b, the couch device 20, and the image processing device 30b to execute dual energy CT imaging, collects projection data, and controls the preprocessing unit 34 to correct the projection data. (Step S21). The X-ray CT apparatus 1b performs dual energy CT imaging by a two-rotation method, for example. In the two-rotation method, at each imaging position in the body axis direction, the first projection data is obtained by rotating the rotating frame 15 once with the first tube voltage applied to the X-ray tube 121b, This is an imaging method in which the second projection data is acquired by rotating the rotating frame 15 once with the second tube voltage applied to the X-ray tube 121b. Since the X-ray CT apparatus 1b is a dual energy CT apparatus, each point of the projection data includes information on the intensity of the X-ray transmitted through the subject P.
The image reconstruction unit 36 reconstructs the projection data stored in the data storage unit 35 and generates a CT image (step S22). Specifically, the first projection data is reconstructed to generate a first CT image, and the second projection data is reconstructed to generate a second CT image. Therefore, the CT image generated by the image reconstruction unit 36 includes a first CT image and a second CT image. The control unit 38b performs various processes on the CT image generated in step S22, that is, the first CT image and the second CT image, and generates image data of a substance to be distinguished (step S23). The display unit 32 displays a CT image and a display image indicating the density distribution of the substance to be discriminated (step S24). For example, the display unit 32 displays three images, that is, an image obtained by adding the first CT image and the second CT image, the first CT image, and the second CT image, and the display image is superimposed on these images. The details of step S23 are as described below.
The deriving unit 381b generates a CT image for deriving constraint conditions from the first CT image and the second CT image (step S201). Specifically, the deriving unit 381b generates a constraint condition deriving CT image by taking the average of the first CT image and the second CT image. Since the CT image for deriving the constraint condition is an image obtained by taking the average of the first CT image and the second CT image, the influence of noise is reduced. The constraint condition derivation CT image may be generated by taking the root mean square of the first CT image and the second CT image.
The calculation formula deriving unit 382b derives a calculation formula for calculating the effective distance of the substance to be discriminated (step S202). Specifically, the calculation formula deriving unit 382b derives a calculation formula for calculating the effective distance of the substance to be distinguished from each of the first projection data and the second projection data. As a calculation formula for calculating the effective distance of the substance, for example, a formula similar to the formula (2) described above can be given.
The deriving unit 381b derives a constraint condition (step S203). That is, the deriving unit 381b derives the constraint condition using at least two pieces of projection data among the plurality of projection data. A specific method for deriving the constraint condition by the deriving unit 381b is as described below.
For example, the deriving unit 381b derives the constraint condition from the CT image for deriving the constraint condition. Examples of the constraint condition include an expression similar to the above-described expression (3) and an expression similar to the expression (5). Alternatively, the deriving unit 381b may derive the constraint condition from the first projection data and the second projection data that have the least influence of noise. For example, the larger the number of photons, the smaller the influence of noise. Thereby, since the influence of noise is reduced as the number of photons is increased, it is possible to suppress deterioration in the accuracy of substance discrimination due to noise.
The calculation unit 383 calculates the effective distance of the substance to be discriminated (step S204). Next, the calculation unit 383 determines whether or not the processing in steps S202 to S204 has been performed on all points on the projection data (step S205). When the processing of step S202 to step S204 has not been performed at all points on the projection data (No at step S205), the process returns to step S202. If the processing of step S202 to step S204 has been performed at all points on the projection data (Yes at step S205), the process proceeds to step S206.
The calculation unit 383 reconstructs the effective distance of the substance to be discriminated and calculates information regarding the substance to be discriminated (step S206). Specifically, the calculation unit 383 reconstructs the effective distance L 1 of the iodine contrast agent I and the effective distance L 3 of the water W, and calculates the density distribution of the iodine contrast agent I and the density distribution of the water W.
The generation unit 384 generates image data of the substance to be discriminated (step S207). Specifically, the generation unit 384 generates image data that is data for displaying the density distribution of the iodine contrast medium I and the density distribution of the water W superimposed on the CT image. The image data is transmitted to the display unit 32, and the display unit 32 displays the CT image, the display image of the iodine contrast medium I and the display image of the water W superimposed on the CT image.
Heretofore, an example of processing of the X-ray CT apparatus 1b according to the second embodiment has been described. As described above, the X-ray CT apparatus 1b uses the calculation formula derived from the first projection data and the second projection data under the constraint condition derived from the constraint condition derivation CT image. distance L 1 and calculating the effective distance L 3 of water W. The effective distances L 1 and L 3 are calculated under the constraint condition derived from the constraint condition derivation CT image in which the influence of noise is reduced. For this reason, X-ray CT apparatus 1b which concerns on 2nd Embodiment can suppress that the precision of substance discrimination falls by noise. Further, it is preferable that the constraint condition is derived from projection data in which the influence of noise is not maximum. Thereby, the X-ray CT apparatus 1b according to the second embodiment calculates the effective distance of the substance to be discriminated under the constraint condition derived from the projection data in which the influence of the noise is not the maximum, so that the influence of the noise is the maximum. It can suppress that the precision of substance discrimination falls by projection data which is.
In addition, the second embodiment has been described by taking dual-rotation type dual energy CT imaging as an example, but the method of dual energy CT imaging is not particularly limited. The above-described contents can be applied to, for example, dual energy CT imaging using a high-speed switching method, a two-tube method, a two-layer detector method, or the like. The high-speed switching method is an imaging method in which the voltage supplied to the X-ray tube is switched at high speed for each view, and high-voltage projection data and low-voltage projection data are alternately acquired during one rotation of the rotating frame. is there. In the two-tube method, an X-ray tube to which a high voltage is supplied and an X-ray tube to which a low voltage is supplied are provided, and high-voltage projection data and low-voltage projection data are provided while the rotating frame rotates once. This is an imaging method for simultaneously acquiring images. The two-layer detector system is a two-layer X-ray detector that detects low energy X-rays with a detector closer to the X-ray tube, and a detector farther away from the X-ray tube. In this imaging method, high-energy X-rays are detected.
Further, the high voltage generator 111a supplies three or more tube voltages having different values to the X-ray tube 121b, and irradiates the subject P with three or more types of X-rays having different energy distributions, in the body axis direction. At each imaging position, imaging may be performed by rotating the rotating frame 15 three or more times.
In the first embodiment, water W, iodinated contrast medium I and gadolinium contrast medium G are exemplified as substances to be distinguished, and in the second embodiment, water W and iodine contrast medium I are exemplified as substances to be distinguished. However, the substances to be distinguished are not limited to these. For example, calcium, muscle, and fat can be given as other examples of substances to be discriminated. In addition, the operator may select the substance to be discriminated by operating the input unit 31.
In the first embodiment and the second embodiment, as described above, the method of analytically calculating the effective distance of the substance to be discriminated using Equation (2) or the like has been described as an example. The method for calculating the effective distance of the substance to be performed is not particularly limited. For example, the effective distance of the substance to be discriminated may be calculated using at least one of the first constraint condition and the second constraint condition and the following equation (6). Equation (6) is such that the sum of the squares of the differences between the number of photons detected by the X-ray detector and the estimated value of the number of photons detected by the X-ray detector is minimized. This means that the effective distance of the substance to be calculated is calculated.
In the second embodiment, the constraint condition is derived from the CT image generated by reconstructing the projection data, but the reconstruction of the projection data is not an essential process. For example, without reconstructing projection data, the projection data may be binarized, and the transmission total distance as a constraint may be derived from the luminance of each point of the binarized projection data.
Finally, embodiments other than the first embodiment and the second embodiment described above will be described.
In 1st Embodiment and 2nd Embodiment, although the case where X-ray CT apparatus performed various processes was demonstrated, embodiment is not restricted to this. For example, an image processing system including an X-ray CT apparatus and an image processing apparatus may execute the various processes described above. Here, the image processing device is, for example, a workstation, an image storage device (image server) of a PACS (Picture Archiving and Communication System), a viewer, various devices of an electronic medical record system, or the like. In this case, for example, the X-ray CT apparatus collects projection data and the like. On the other hand, the image processing apparatus receives projection data or the like collected by the X-ray CT apparatus from the X-ray CT apparatus or the image server via a network, or is input from an operator via a recording medium. Is stored in the storage unit. Then, the image processing apparatus may perform the various processes described above for the projection data stored in the storage unit.
The instructions shown in the processing procedure shown in the above-described embodiment can be executed based on a program that is software. A general-purpose computer stores this program in advance and reads this program, so that the same effect as that obtained by the X-ray CT apparatus of the above-described embodiment can be obtained. The instructions described in the above-described embodiments are, as programs that can be executed by a computer, magnetic disks (flexible disks, hard disks, etc.), optical disks (CD-ROM, CD-R, CD-RW, DVD-ROM, DVD). ± R, DVD ± RW, etc.), semiconductor memory, or a similar recording medium. As long as the computer or embedded system can read the storage medium, the storage format may be any form. If the computer reads the program from the recording medium and causes the CPU to execute instructions described in the program based on the program, the same operation as the X-ray CT apparatus of the above-described embodiment can be realized. . Further, when the computer acquires or reads the program, it may be acquired or read through a network.
The OS (Operating System), database management software, MW (Middleware) such as a network, etc. running on the computer based on the instructions of the program installed in the computer or embedded system from the storage medium realize the above-described embodiment. A part of each process for performing may be executed. Furthermore, the storage medium is not limited to a medium independent of a computer or an embedded system, but also includes a storage medium in which a program transmitted via a LAN (Local Area Network) or the Internet is downloaded and stored or temporarily stored. Further, the number of storage media is not limited to one, and the processing in the embodiment described above is executed from a plurality of media, and the configuration of the medium may be any configuration included in the storage medium in the embodiment. .
FIG. 18 is a diagram illustrating a hardware configuration of an image processing apparatus according to an embodiment other than the first embodiment and the second embodiment. The image processing apparatus according to the above-described embodiment is connected to a control device such as a CPU (Central Processing Unit) 40, a storage device such as a ROM (Read Only Memory) 50 and a RAM (Random Access Memory) 60, and a network. A communication I / F 70 that performs communication and a bus 80 that connects each unit are provided.
A program executed by the image processing apparatus according to the above-described embodiment is provided by being incorporated in advance in the ROM 50 or the like. The program executed by the image processing apparatus according to the above-described embodiment can cause a computer to function as each unit of the above-described image processing apparatus. In this computer, the CPU 40 can read and execute a program from a computer-readable storage medium onto a main storage device.
According to the X-ray CT apparatus and image processing apparatus of at least one embodiment described above, substance discrimination can be performed with higher accuracy.
382a derivation unit 383 calculation unit 384 generation unit
An X-ray tube that generates X-rays;
An X-ray detector having a plurality of X-ray detection elements that output signals based on the incident X-rays;
A derivation unit that derives a constraint condition using at least one projection data among a plurality of projection data in which at least a part of the corresponding energy band is different;
Using the projection data and the constraint condition, an effective distance that is the sum of the distances that the X-rays emitted from the X-ray tube and incident on the X-ray detection element pass through the region where the substance to be discriminated exists is obtained. A calculation unit for calculating,
A generating unit that generates image data for displaying information on the substance using the projection data and the effective distance;
Using the signal, collecting the counting information, which is information in which the position of the X-ray tube, the position of the X-ray detection element on which the photons are incident, the energy of the photons and the count value of the photons are associated with each other, and the counting A collection unit that collects the plurality of projection data using information;
2. The X-ray CT apparatus according to claim 1, wherein the calculation unit calculates the effective distance using projection data obtained by adding the constraint condition and a count value of photons at each point of at least two projection data.
A high voltage generator for supplying a plurality of different tube voltages to the X-ray tube;
A collecting unit for collecting the plurality of projection data by collecting the intensity of a plurality of X-rays having different energy distributions generated by the plurality of tube voltages;
The X-ray CT apparatus according to claim 1, wherein the deriving unit derives the constraint condition using at least two projection data among the plurality of projection data.
The derivation unit calculates a transmission total distance at each point of the projection data used for calculating the effective distance from a CT image obtained by reconstructing the projection data used for derivation of the constraint condition,
The said generation part produces | generates the image data for displaying the information regarding the said substance to discriminate | determine based on the projection data used for calculation of the said effective distance, and the said transmission total distance. The X-ray CT apparatus according to one.
The derivation unit calculates the existence probability of the substance to be distinguished at each point of the projection data used for calculating the effective distance from the CT image obtained by reconstructing the projection data used for derivation of the constraint condition,
The said production | generation part produces | generates the image data for displaying the information regarding the said substance to discriminate | determine based on the projection data used for calculation of the said effective distance, and the said existence probability. X-ray CT apparatus described in 1.
An input unit for selecting the constraint condition;
The derivation unit derives the constraint condition selected via the input unit from the CT image obtained by reconstructing the projection data used to derive the constraint condition,
The X-ray CT apparatus according to claim 1, wherein the generation unit generates image data for displaying information related to the substance based on the constraint condition.
The range in which all energy bands corresponding to the projection data used when the derivation unit derives the constraint condition is combined with all ranges corresponding to the projection data used when the calculation unit calculates the effective distance. The X-ray CT apparatus according to claim 1, wherein the X-ray CT apparatus is wider than a combined range of energy bands.
The range of all energy bands corresponding to the projection data used when the calculation unit calculates the effective distance is set based on the constraint condition. X-ray CT apparatus described in 1.
A deriving unit for deriving a constraint condition using at least one projection data among a plurality of projection data having different X-ray energy bands;
The distance that the X-rays emitted from the X-ray tube and incident on the X-ray detection element are transmitted through the region where the substance to be discriminated exists using at least one of the plurality of projection data and the constraint condition. A calculation unit for calculating an effective distance that is a sum of
A generating unit for generating image data for displaying information on the substance from the effective distance;
A derivation procedure for deriving a constraint condition using at least one projection data among a plurality of projection data in which at least a part of the corresponding energy band is different;
Using the projection data and the constraint conditions, the X-ray emitted from the X-ray tube and incident on the X-ray detection element of the X-ray detector is the total distance transmitted through the region where the substance to be discriminated exists. A calculation procedure for calculating the effective distance;
A generation procedure for generating image data for displaying information on the substance using the effective distance and the projection data;
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