JP6129517B2 - X-ray diagnostic apparatus and control program - Google Patents

X-ray diagnostic apparatus and control program Download PDF

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JP6129517B2
JP6129517B2 JP2012244473A JP2012244473A JP6129517B2 JP 6129517 B2 JP6129517 B2 JP 6129517B2 JP 2012244473 A JP2012244473 A JP 2012244473A JP 2012244473 A JP2012244473 A JP 2012244473A JP 6129517 B2 JP6129517 B2 JP 6129517B2
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image data
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JP2014090960A (en
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高橋 章仁
章仁 高橋
白石 邦夫
邦夫 白石
坂田 充
充 坂田
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東芝メディカルシステムズ株式会社
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Description

  Embodiments described herein relate generally to an X-ray diagnostic apparatus capable of selectively collecting high-definition image data in an examination target region of a subject.

  Medical image diagnosis using an X-ray diagnostic apparatus, an MRI apparatus, an X-ray CT apparatus, etc. has made rapid progress with the development of computer technology and has become indispensable in today's medical care. In particular, the X-ray imaging diagnosis of the circulatory region, which has been progressing with the development of the catheter technique, is intended for the entire arteries and veins including the cardiovascular system. Usually, the X-ray of the vascular region to which a contrast medium has been administered. This is performed by observing fluoroscopic image data collected by photographing.

  For example, an X-ray diagnostic apparatus for the purpose of diagnosing a circulatory region includes an X-ray generation unit and an X-ray detection unit (hereinafter collectively referred to as an imaging system), a holding unit that holds the imaging system, and a subject. And the C-arm provided on the above-described top plate and the holding portion are moved in a desired direction, so that X-ray imaging from the optimum direction can be performed on the subject. .

  The spatial resolution of the X-ray diagnostic apparatus described above is usually determined by the width of the detection elements provided in the X-ray detection unit, the arrangement interval, and the like, and a thin blood vessel using the X-ray detection unit having a standard spatial resolution. In addition, when imaging a fine intravascular device such as a stent inserted into these blood vessels, it is often difficult to obtain image data having sufficient resolution.

  In order to solve such problems, in addition to the X-ray detector, a high-definition X-ray detector that enables high resolution in a narrow imaging region is separately provided, and the X-ray detector is used. When the spatial resolution of the precision inspection area that requires particularly precise inspection is insufficient in the generated image data, the X-ray detection section is switched to the high-definition X-ray detection section and used to improve the quality in the precision inspection area. A method for collecting simple image data has been proposed.

  On the other hand, CMOS (Complementary Metal Oxide Semiconductor) image sensors are image sensors that are widely used in consumer digital cameras and the like, and are equipped with a system-on-chip structure in which a sensor unit, pixel amplifier, and the like are integrated. Since non-destructive readout is possible, it is being used instead of a conventional thin film transistor (TFT) as an X-ray detection element of an X-ray diagnostic apparatus that enables high-speed X-ray imaging.

JP 2008-229270 A

  According to the conventional method described above, a high-definition X-ray detection unit that has a fine X-ray detection element and can capture a relatively narrow area with high spatial resolution is used selectively. Good image data in the inspection area or the like can be easily obtained.

However, in the X-ray detection element provided in the high-definition X-ray detection unit, the imaging region is narrow as described above, and the detection element interval (that is, the pixel interval) is small, so that the inspection target region is within the X-ray irradiation period. In the case of moving in (1), a positional shift similar to that in the case of using a standard X-ray detection unit occurs, so that it becomes impossible to improve the spatial resolution. In addition, since the relative positional shift with respect to each pixel increases, when the narrow-range image data collected by the high-definition X-ray detection unit is enlarged and displayed with a normal display size, the inspection target area is moved. The effect of misalignment caused by the increase is rather increased.
On the other hand, as a method of reducing the above-described positional deviation, a method of shortening the X-ray irradiation period required for one piece of image data can be considered. According to this method, in order to obtain a constant X-ray signal, There is a problem that it is necessary to increase the amount of X-ray irradiation per hour and a large-capacity X-ray tube is required. Further, if the pitch for each pixel is narrowed in order to obtain a high-definition image, the amount of charge that can be stored in each pixel is essentially reduced, so that the S / N of the image is deteriorated. In order to compensate for this, it is necessary to prepare an X-ray tube with a larger capacity than in the case of the X-ray detector.

  The present disclosure has been made in view of such a conventional problem, and the purpose thereof is to generate high-definition image data using an X-ray detection unit having a plurality of fine detection elements. Collecting a plurality of sub-image data in a predetermined imaging period by increasing the reading speed of the signal charge accumulated in the X-ray detection unit, and performing positional deviation correction and addition synthesis on these sub-image data An X-ray diagnostic apparatus and a control program capable of collecting high-definition image data having better sensitivity and spatial resolution.

In order to solve the above problems, an X-ray diagnostic apparatus of the present disclosure, when cormorants row in the X-ray predetermined shooting period capturing of high-resolution imaging mode to the subject, and the accumulation of charge in the predetermined shooting period X-ray imaging means for generating a plurality of high-definition projection data by performing charge readout a plurality of times, and generating a plurality of sub-image data for the predetermined imaging period based on each of the plurality of high-definition projection data Sub image data generation means; relative position deviation of the plurality of sub image data; and position deviation correction means for correcting the position deviation based on these detection results; and the plurality of position deviation corrected and synthesis processing means for generating a high-definition image data of one frame in the predetermined shooting period by adding synthesizing sub-image data, and displays the high resolution image data It is characterized in that a Display means.

1 is a block diagram showing the overall configuration of an X-ray diagnostic apparatus in the present embodiment. The block diagram which shows the specific structure of the X-ray imaging part with which the X-ray diagnostic apparatus of this embodiment is provided. 4 is a time chart for explaining a method for generating high-definition image data based on a plurality of sub-image data collected by X-ray imaging in a high-definition imaging mode in the present embodiment. 5 is a flowchart showing a procedure for collecting high-definition image data in the present embodiment. The time chart for demonstrating the production | generation method of the high-definition image data in the modification of this embodiment. The block diagram which shows the specific structure of the high-definition image data generation part in the modification of this embodiment.

  Hereinafter, embodiments of the present disclosure will be described with reference to the drawings.

(Embodiment)
In the X-ray imaging in the high-definition imaging mode in this embodiment, first, a plurality of X-ray irradiations and charges are performed using a high-definition X-ray detection unit having a CMOS image sensor or the like that can read charges at high speed with a narrow element spacing. Accumulation and charge readout are performed during a predetermined imaging period, and a plurality of sub-image data is collected. Next, relative positional deviation between the sub-image data is detected, and high-definition image data is generated by adding and synthesizing the plurality of sub-image data corrected for positional deviation based on the detection result.

  In the following, an X-ray diagnostic apparatus applied to the examination of the circulatory region will be described. However, an X-ray diagnostic apparatus for the purpose of examining other areas such as the abdomen may be used.

(Configuration and function of the device)
The configuration and functions of the X-ray diagnostic apparatus according to this embodiment will be described with reference to FIGS. FIG. 1 is a block diagram showing an overall configuration of the X-ray diagnostic apparatus according to the present embodiment, and FIG. 2 is a block diagram showing a specific configuration of an X-ray imaging unit provided in the X-ray diagnostic apparatus. .

  An X-ray diagnostic apparatus 100 shown in FIG. 1 includes an imaging mode using a standard X-ray detector 3a (hereinafter referred to as a standard imaging mode) and a high-definition X-ray detector for an examination target region of a subject 300. An X-ray imaging unit 1 that emits X-rays in an imaging mode using 3b (hereinafter referred to as a high-definition imaging mode), detects X-rays transmitted through the region to be inspected, and generates projection data; X-ray generation unit 2 that performs X-ray irradiation, X-ray detection unit 3a that performs X-ray detection, and holding unit 6 such as a C-arm that holds an imaging system having a high-definition X-ray detection unit 3b, and a subject 300 The top plate 7 on which the imaging system is mounted, the holding unit 6 to which the above-described imaging system is attached, the top plate 7 on which the subject 300 is mounted, and the high-definition X-ray detection unit 3b of the imaging system are placed at a desired position. The moving mechanism unit 8 to be moved to the standard imaging mode output from the X-ray imaging unit 1 The standard image data generation unit 9a that generates standard image data using the data (standard projection data), and the high-definition imaging mode projection data (high-definition projection data) output from the X-ray imaging unit 1 are processed to be high. A high-definition image data generation unit 9b that generates fine-image data and a display unit 10 that displays the obtained standard image data and high-definition image data are further provided. Further, input of subject information, selection of an imaging mode, X-ray An input unit 11 for setting irradiation conditions, setting of image data generation conditions, inputting various instruction signals, and the like, and a system control unit 12 for comprehensively controlling each unit described above are provided.

  As shown in FIG. 1, the X-ray imaging unit 1 includes an X-ray generation unit 2 that irradiates a subject 300 with X-rays, an X-ray detection unit 3 a that detects X-rays that have passed through the subject 300, and a high definition. X-ray detection unit 3b, standard projection data generation unit 4a that generates standard projection data based on transmission X-ray information detected by X-ray detection unit 3a, and transmission X detected by high-definition X-ray detection unit 3b A high-definition projection data generation unit 4b that generates high-definition projection data based on the line information and a high-voltage generation unit 5 that supplies a high voltage to the X-ray generation unit 2 are provided in the examination target region of the subject 300. On the other hand, it has a function of performing X-ray imaging in the standard imaging mode and X-ray imaging in the high-definition imaging mode. In this case, an imaging system (first imaging system) in the standard imaging mode is formed by combining the X-ray generation unit 2 and the X-ray detection unit 3a, and the X-ray generation unit 2 and the high-definition X-ray detection unit 3b are combined. Thus, an imaging system (second imaging system) in the high-definition shooting mode is formed.

  FIG. 2 is a block diagram showing a specific configuration of each of the above-described units provided in the X-ray imaging unit 1. The X-ray generation unit 2 irradiates the examination target region of the subject 300 with X-rays. An X-ray tube 21 and a movable aperture 22 that forms an X-ray weight (cone beam) within a predetermined range with respect to the X-rays emitted from the X-ray tube 21. The X-ray tube 21 is a vacuum tube that generates X-rays, and thermoelectrons generated from a heated cathode (filament) are accelerated by a high voltage supplied from the high-voltage generating unit 5 and collide with a tungsten anode to generate X-rays. generate.

  On the other hand, the movable diaphragm 22 is used for the purpose of reducing the exposure dose to the subject 300 and improving the image quality of the image data, and an upper blade that narrows the X-rays emitted from the X-ray tube 21 into a predetermined irradiation range; Lower blades that reduce scattered radiation and leakage dose by moving in conjunction with the upper blades, and compensation filters that prevent halation by selectively reducing X-rays that have passed through a medium with low absorption (both (Not shown).

  In particular, the position of the X-ray irradiation range in the high-definition imaging mode in the present embodiment is controlled based on the area information of the high-definition X-ray detection unit 3b that is moved by a detection unit moving mechanism 81 described later provided in the movement mechanism unit 84. The exposure dose to the subject 300 can be reduced by limiting the X-ray irradiation range to a relatively narrow area of the high-definition X-ray detection unit 3b, which is determined by the diaphragm blades of the movable diaphragm 22 Become.

  Next, the X-ray detector 3a of the present embodiment used in the standard imaging mode includes a standard X-ray detector 31 that detects X-rays that have passed through the subject 300 as shown in FIG. Has a gate driver 32 for supplying a drive signal for reading out as a signal charge to the standard X-ray detector 31.

  The standard X-ray detector 31 has a scintillator that converts incident X-rays into visible light, and has a structure in which a TFT (thin film transistor) is disposed behind the scintillator. The TFT includes two-dimensionally arranged pixels, each of which includes a photoelectric conversion unit such as a photodiode, a charge storage capacitor that stores signal charges generated by the photoelectric conversion unit, and a signal stored in the charge storage capacitor. A TFT (thin film transistor) (both not shown) for reading out charges at a predetermined timing is provided.

  In the following, an indirect conversion type standard X-ray detector 31 having a scintillator that once converts incident X-rays into visible light as described above will be described. However, a photoconductor is provided to convert X-rays directly into charge signals. A direct conversion type standard X-ray detector 31 for conversion may be used.

  The standard projection data generation unit 4a includes, for example, a charge / voltage converter 41 that converts signal charges read from the standard X-ray detector 31 in parallel in units of line directions into voltages, and a charge / voltage converter. A / D converter 42 for generating projection data elements by converting the output of 41 into a digital signal, and a parallel / serial converter for converting the obtained projection data elements into time-series data elements 43. The data elements of the projection data output in time series from the parallel / serial converter 43 are supplied to the standard image data generation unit 9a in FIG.

  On the other hand, the high-definition X-ray detection unit 3b and the high-definition projection data generation unit 4b used in the high-definition imaging mode have substantially the same configuration as the X-ray detection unit 3a and the standard projection data generation unit 4a. However, instead of the TFT included in the standard X-ray detector 31 of the X-ray detector 3a, for example, a two-dimensional image sensor using a complementary metal oxide semiconductor (CMOS) transistor (hereinafter referred to as a CMOS image sensor). ).

  Since the CMOS image sensor can be easily integrated with an amplifier corresponding to each detection element, a processing circuit for parallel output, and the like, the reading speed can be greatly improved. The data elements of the high-definition projection data output in time series from the high-definition projection data generation unit 4b are supplied to the high-definition image data generation unit 9b in FIG.

  Returning to FIG. 1, the high voltage generator 5 includes a high voltage generator 52 that generates a high voltage to be applied between the anode and the cathode in order to accelerate the thermal electrons generated from the cathode of the X-ray tube 21. The tube current, tube voltage, X-ray irradiation time, X-ray irradiation cycle in the high voltage generator 52 based on the X-ray irradiation conditions and the imaging timing signal in the standard imaging mode and high-definition imaging mode supplied from the system control unit 12; A high voltage control unit 51 for controlling the X-ray irradiation timing and the like is provided.

  Next, the moving mechanism unit 8 causes the high-definition X-ray detection unit 3b to move to a desired region (that is, in the inspection target region observed by X-ray imaging in the standard imaging mode using the X-ray detection unit 3a). A detection unit moving mechanism 81 that moves to a region that requires a particularly precise inspection (precision inspection region), an X-ray generation unit 2, an X-ray detection unit 3a, and a high-definition X-ray detection unit 3b (first imaging system). And a holding unit moving mechanism 82 for rotating or moving the holding unit 6 to which the second imaging system is attached around the subject 300, and the top plate 7 in the body axis direction of the subject 300 (z direction in FIG. 1). ) And the top plate moving mechanism 83 that moves in the direction orthogonal to the body axis (the x direction and the y direction in FIG. 1), and the diaphragm blades of the movable diaphragm 22 provided in the X-ray generator 2 are moved to predetermined positions. A diaphragm moving mechanism (not shown), the above-described detecting unit moving mechanism 81, and holding unit moving Structure 82, and a moving mechanism control unit 84 for controlling the stage move mechanism 83 and the aperture movement mechanism.

  Then, the movement mechanism control unit 84 generates, for example, a movement control signal generated based on the detection unit movement instruction signal supplied from the input unit 11 via the system control unit 12 under the observation of the standard image data. 81, the high-definition X-ray detection unit 3b is moved to the precision inspection region by supplying to 81, and the movement control signal generated based on the imaging system movement instruction signal supplied from the input unit 11 is sent to the holding unit moving mechanism 82. An imaging position and an imaging direction suitable for the X-ray imaging are set by rotating or moving the holding unit 6 to which the imaging system is attached around the subject 300.

  Similarly, the movement mechanism control unit 84 supplies the movement control signal generated based on the table movement instruction signal supplied from the input unit 11 to the table movement mechanism 83 and causes the table 6 to be attached to the body of the subject 300. The center of the region to be inspected is set by parallel movement in the axial direction or the direction orthogonal to the body axis, and a movement control signal generated based on the detection unit movement instruction signal is supplied to a diaphragm movement mechanism (not shown). As a result, the plurality of diaphragm blades provided in the movable diaphragm 22 of the X-ray generation unit 2 are moved to a region corresponding to the high-definition X-ray detection unit 3b.

  Note that a specific arrangement method of the high-definition X-ray detection unit 3b with respect to the precision inspection region is described in the above-described Patent Document 1 and the like, and thus detailed description thereof is omitted.

  Next, the standard image data generation unit 9a includes, for example, a projection data storage unit and an image data processing unit (not shown), and in time series from the standard projection data generation unit 4a of the X-ray imaging unit 1 in X-ray imaging in the standard imaging mode. The data elements of the standard projection data that are output automatically are sequentially stored in the projection data storage unit in correspondence with the line direction and the column direction of the detection elements to generate standard image data. The image data processing unit performs image processing such as filtering processing on the standard image data read from the projection data storage unit as necessary, and supplies the processed standard image data to the display unit 10.

  On the other hand, the high-definition image data generation unit 9b includes a plurality of pre-combination image data (hereinafter referred to as sub-images) by X-ray imaging in a high-definition imaging mode using the high-definition X-ray detection unit 3b capable of high-speed reading. Data) is collected during a predetermined shooting period (that is, a period during which one standard image data or high-definition image data is collected), and positional deviation correction and addition synthesis are performed on these sub-image data. Therefore, it has a function to generate high-definition image data with excellent spatial resolution and sensitivity.

  That is, the high-definition image data generation unit 9b includes a sub-image data generation unit 91, an image data synthesis unit 92, and an image data processing unit 93 as shown in FIG. The data elements of the high-definition projection data output in time series from the high-definition projection data generation unit 4b of the unit 1 are sequentially stored in a projection data storage unit (not shown) of the sub-image data generation unit 91, and the above-described sub-image data is stored. Generated.

  The image data synthesis unit 92 includes a position deviation correction unit 921 and a synthesis processing unit 922. First, the positional deviation correction unit 921 reads out a plurality of sub image data collected in the above-described photographing period and stored in the projection data storage unit of the sub image data generation unit 91, and for example, a pattern is read from these sub image data. A relative positional shift between the sub-image data is detected by performing cross-correlation processing such as matching. Next, the position shift of the remaining sub image data with respect to the reference sub image data selected from the plurality of sub image data is corrected based on the position shift detection result. On the other hand, the composition processing unit 922 generates high-definition image data by adding and synthesizing a plurality of sub-image data corrected for positional deviation.

  Next, the image data processing unit 93 performs image processing such as filtering processing on the high-definition image data supplied from the image data combining unit 92 as necessary, and displays the processed high-definition image data on the display unit 10. To supply.

  Next, X-ray imaging in high-definition imaging mode and generation of high-definition image data based on sub-image data collected by this X-ray imaging will be described with reference to the time chart of FIG.

  FIG. 3 compares X-ray imaging in the standard imaging mode and X-ray imaging in the high-definition imaging mode. FIGS. 3A to 3C show the X-ray irradiation period, the charge in the standard imaging mode. The accumulation / readout period and the standard image data generation period are shown in FIGS. 3D to 3G, and X in the high-definition shooting mode corresponding to the periods shown in FIGS. 3A to 3C. A line irradiation period, a charge accumulation / readout period, a sub-image data generation period, and a high-definition image data generation period are shown.

  However, in FIG. 3, each of the charge accumulation period and the charge readout period in the X-ray imaging in the high-definition imaging mode is shortened to about ½ of the charge accumulation period and the charge readout period in the X-ray imaging in the standard imaging mode. However, the shortening rate of the charge accumulation period and the charge readout period in the high-definition imaging mode is not limited to ½, and the shortening rate of the charge accumulation period and the charge readout period The shortening rate may be different. Such shortening of the charge accumulation period and the charge readout period can be easily realized by using the high-definition X-ray detection unit 3b having the CMOS image sensor as described above.

  That is, in the X-ray imaging in the standard imaging mode, the irradiation period αx and the irradiation based on the times t10, t20, t30,... As shown in FIG. X-ray irradiation with a period (imaging period) Tx is repeatedly performed by the high voltage generation unit 5 and the X-ray generation unit 2, and the periods [t10 to t11] and [t20 to [t20] in FIG. Accumulation of signal charges at t21],... and readout of signal charges at periods [t11 to t20], [t21 to t30],. Then, the generation of the standard projection data and the standard image data based on the signal charges by the standard projection data generation unit 4a and the standard image data generation unit 9a is based on the times t20, t30,. In the period βx.

  On the other hand, in the X-ray imaging in the high-definition imaging mode, an irradiation period based on times t10, ta1b, t20, ta2b,... As shown in FIG. The X-ray irradiation of αa and irradiation period (imaging period) Ta is repeated by the high voltage generator 5 and the X-ray generator 2, and the periods [t10 to ta11] and [t11] in FIG. Accumulation and periods [ta11 to ta12], [ta13 to t20], [ta21 to ta22], [ta23 to t30] of ta12 to ta13], [t20 to ta21], [ta22 to ta23],. ,... Are read by the high-definition X-ray detector 3b.

  Then, the generation of the high-definition projection data and the sub-image data based on the read charges by the sub-image data generation unit 91 of the high-definition projection data generation unit 4b and the high-definition image data generation unit 9b is shown in FIG. This is performed in a period γa based on the times ta12, t20, ta22, t30,..., And the subimage data of ta12 and that of t20 are synthesized by the image data synthesis unit 92 at time t20 in FIG. The Similarly, at t30, the sub-image data of ta22 and that of t30 are combined. In this case, in the period βa based on the times t20, t30,..., The position shift detection by the comparative evaluation of the sub image data and the position shift correction based on the detection result are performed by the position shift correction unit of the image data combining unit 92. The composition processing unit 922 synthesizes the corrected sub image data.

  Returning to FIG. 1 again, the display unit 10 includes a display data generation unit, a data conversion unit, and a monitor (not shown). The display data generation unit generates the standard image data and the high-definition image generated by the standard image data generation unit 9a. After the high-definition image data generated in the data generation unit 9b is converted into a predetermined display format, display data is generated by adding subject information and various examination information, and the data conversion unit adds the display data to the display data. On the other hand, conversion processing such as D / A conversion and television format conversion is performed and displayed on the monitor.

  The display data generation unit described above may generate display data by superimposing or arranging standard image data and high-definition image data in parallel, or may generate display data for each of these image data. Also good. In this case, it is desirable to set the enlargement ratio of the high-definition image data larger than the enlargement ratio of the standard image data, but there is no particular limitation.

  The input unit 11 is an interactive interface including input devices such as a display panel, a keyboard, a trackball, a joystick, and a mouse. The input unit 11 inputs subject information, selects a standard imaging mode and a high-definition imaging mode, and each imaging mode. X-ray irradiation conditions (tube current, tube voltage, X-ray irradiation time, X-ray irradiation cycle, X-ray irradiation timing, etc.), X-ray imaging conditions setting, image data generation conditions and image data display conditions setting, precision inspection Various setting signals such as area setting, detection unit movement instruction signal, imaging system movement instruction signal, and top board movement instruction signal are input.

  The system control unit 12 includes a CPU and an input information storage unit (not shown), and various information input / set / selected by the input unit 11 is stored in the input information storage unit. Then, the CPU comprehensively controls the above-described units of the X-ray diagnostic apparatus 100 based on these pieces of information, and generates / displays standard image data by X-ray imaging in the standard imaging mode and in the high-definition imaging mode. Generation / display of high-definition image data by X-ray imaging is executed. In particular, in the high-definition imaging mode, positional deviation correction and composition processing are performed on a plurality of sub-image data collected using the high-definition X-ray detection unit 3b that has a high signal charge readout speed and a narrow array of detection elements. By doing so, it is possible to generate high-definition image data with excellent spatial resolution and sensitivity.

(High-resolution image data collection procedure)
Next, a procedure for collecting high-definition image data using the high-definition X-ray detection unit 3b capable of reading signal charges at high speed will be described with reference to the flowchart of FIG.

  Prior to the collection of high-definition image data, a medical worker such as a doctor or an inspector who operates the X-ray diagnostic apparatus 100 (hereinafter collectively referred to as an operator) uses the input unit 11 to obtain subject information. After the input, X-ray irradiation conditions, X-ray imaging conditions, image data generation conditions, and image data display conditions in the standard imaging mode and high-definition imaging mode are set, and these input information and setting information are set in the system control unit 12. The data is stored in the input information storage unit (step S1 in FIG. 4).

  When the above initial setting is completed, the operator places the top 7 on which the subject 300 is placed and the first imaging system (X-ray generation unit 2 and X-rays) provided around the subject 300. The imaging position and the imaging direction in the standard imaging mode for the subject 300 are set by moving / rotating the holding unit 6 holding the detection unit 3a) in a predetermined direction (step S2 in FIG. 4).

  Next, the operator selects a standard photographing mode and inputs a photographing start instruction signal at the input unit 11, and this instruction signal is supplied to the system control unit 12, thereby performing standard photographing using the first imaging system. Mode X-ray imaging is started (step S3 in FIG. 4).

  That is, the system control unit 12 supplies the X-ray irradiation conditions in the standard imaging mode read from its own input information storage unit and an instruction signal for generating X-rays to the high voltage control unit 51 of the high voltage generation unit 5. The high voltage control unit 51 that has received this instruction signal controls the high voltage generator 52 based on the X-ray irradiation conditions and applies a high voltage to the X-ray tube 21 of the X-ray generation unit 2. Then, the X-ray tube 21 to which the high voltage is applied irradiates the subject 300 with X-rays in the standard imaging mode for a predetermined period via the X-ray restrictor 22, and the X-rays transmitted through the subject 300 are thereafter It is detected by the standard X-ray detector 31 of the X-ray detector 3a provided on the side.

  At this time, the photoelectric film of the detection elements that are two-dimensionally arranged in the standard X-ray detector 31 receives the X-rays that have passed through the subject 300 and accumulates signal charges proportional to the X-ray transmission amount in the charge storage capacitor. To do. When the X-ray irradiation is completed, the gate driver 32 sequentially reads out the signal charges stored in the charge storage capacitor by supplying drive pulses to the TFTs of the standard X-ray detector 31.

  The read signal charges are converted in voltage by the charge / voltage converter 41 of the standard projection data generation unit 4a, converted into a digital signal by the A / D converter 42, and then stored in the buffer memory of the parallel / serial converter 43. Once stored as projection data for one line. Next, the parallel / serial converter 43 reads the data elements of the projection data stored in its own buffer memory serially in line units, and sequentially stores them in the projection data storage unit of the standard image data generation unit 9a, thereby projecting the projection data. Two-dimensional standard image data is generated in the data storage unit. The image data processing unit of the standard image data generation unit 9a performs image processing such as filtering processing on the standard image data read from the projection data storage unit as necessary, and displays the processed standard image data on the display unit. 10 is displayed on the monitor (step S4 in FIG. 4).

  On the other hand, an operator who observes the standard image data displayed on the display unit 10 inputs a precise inspection area that requires a particularly precise inspection from the inspection target area indicated by the standard image data. Setting is performed using the device, and further, a detection unit movement instruction signal for moving the high-definition X-ray detection unit 3b to the fine inspection region is input.

  The movement mechanism control unit 84 of the movement mechanism unit 8 that has received the setting information and the instruction signal via the system control unit 12 supplies the movement control signal generated based on the information to the detection unit movement mechanism 81. Then, the detection unit moving mechanism 81 sets the high-definition X-ray detection unit 3b to the precise inspection region based on this movement control signal (step S5 in FIG. 4).

  When the setting of the high-definition X-ray detection unit 3b for the precision inspection region is completed, the operator selects the high-definition imaging mode and inputs the imaging start instruction signal in the input unit 11, and this instruction signal is the system control unit. 12, the X-ray imaging in the high-definition imaging mode using the second imaging system (X-ray generator 2 and high-definition X-ray detector 3b) is started (step S6 in FIG. 4). .

  That is, according to the same procedure as in step S4 described above, the system control unit 12 generates the high-definition imaging mode X-ray irradiation conditions read from its own input information storage unit and an instruction signal for generating X-rays. The high voltage control unit 51 that is supplied to the high voltage control unit 51 of the unit 5 and receives this instruction signal controls the high voltage generator 52 based on the X-ray irradiation conditions described above to control the X-ray of the X-ray generation unit 2. A high voltage is applied to the tube 21. At this time, the X-ray tube 21 to which a high voltage is applied performs X-ray irradiation in the high-definition imaging mode on the subject 300 a plurality of times at predetermined time intervals, and permeates the subject 300 in each X-ray irradiation. X-rays are detected by a high-definition X-ray detection unit 3b provided behind the X-rays.

  On the other hand, the high-definition projection data generation unit 4b generates high-definition projection data based on the signal charge corresponding to the transmitted X-ray dose detected by the high-definition X-ray detection unit 3b, and the high-definition image data generation unit 9b The sub-image data is generated by storing the high-definition projection data supplied in time series from the high-definition projection data generation unit 4b in units of X-rays in the projection data storage unit included in the own sub-image data generation unit 91. (Step S7 in FIG. 4).

  For example, as shown in FIG. 3, when X-ray irradiation in the high-definition imaging mode is performed twice in the imaging period Tx, the X-ray tube 21 to which a high voltage is applied by the high voltage generator 5 is applied to the X-ray irradiation period αa. The sub-image data generation unit 91 of the high-definition image data generation unit 9b generates high-definition projection data along with the first X-ray irradiation. The first sub-image data is generated by storing the high-definition projection data supplied from the unit 4b in its own projection data storage unit.

  Next, the X-ray tube 21 performs the second X-ray irradiation having the X-ray irradiation period αa in the period [ta1b to ta1c] after Ta from the first X-ray irradiation, and the high-definition image data generation unit 9b The sub-image data generation unit 91 stores the high-definition projection data supplied from the high-definition projection data generation unit 4b in association with the second X-ray irradiation in the projection data storage unit, whereby the second sub-image data Is generated.

  When the generation and storage of a plurality of sub-image data corresponding to a plurality of times of X-ray irradiation performed in one imaging period are completed by such a procedure, the positional deviation correction unit 921 of the image data composition unit 92 A plurality of sub-image data generated during the above-described photographing period and stored in the projection data storage unit of the sub-image data generation unit 91 is read out, and a sub-correlation process such as pattern matching is performed on these sub-image data. A positional shift between data is detected (step S8 in FIG. 4). Then, the positional deviation of the sub image data is corrected based on the obtained positional deviation detection result (step S9 in FIG. 4).

  For example, the positional deviation correction unit 921 extracts reference sub-image data from a plurality of sub-image data read from the projection data storage unit, and detects a positional deviation of other sub-image data with respect to the reference sub-image data. Then, based on the obtained positional deviation detection result, the positional deviation of the other sub image data is corrected.

  Next, the composition processing unit 922 of the image data composition unit 92 generates high-definition image data by adding and synthesizing the plurality of sub-image data corrected for positional deviation, and the image data processing unit 93 includes the image data composition unit 92. The high-definition image data supplied from is subjected to image processing such as filtering processing as necessary and displayed on the monitor of the display unit 10 (step S10 in FIG. 4).

(Modification)
Next, a modification of this embodiment will be described.

  In the above-described embodiment, the case where the X-ray pulse having a short width is irradiated according to the high-speed driving by the high-definition X-ray detection unit has been described. However, in this modification, the high-speed pulse interval or the short-time pulse is irradiated. When using a high-voltage generator and X-ray tube that cannot be used, the X-ray pulse width is equal to or greater than that when using a standard X-ray detector while using the same pulse irradiation interval as when using a standard X-ray detector. A method of synthesizing while performing positional deviation correction using the collected non-destructive readout image within the pulse width will be described.

  That is, in this modification, a CMOS image that can be read nondestructively when reading out signal charges accumulated in each of the detection elements and generating sub-image data and high-definition image data in X-ray imaging in the high-definition imaging mode. Generation of sub-image data and generation of high-definition image data based on the sub-image data when using the high-definition X-ray detection unit 3b having a sensor or the like will be described with reference to FIGS.

  FIG. 5 is a time chart comparing the X-ray imaging in the standard imaging mode and the X-ray imaging in the high-definition imaging mode in the present modification, and the X-ray irradiation period, the charge accumulation / readout period, and the standard in the standard imaging mode. FIGS. 5A to 5C showing the image data generation period are the same as FIGS. 3A to 3C already shown, and the description thereof is omitted.

  On the other hand, FIGS. 5D to 5G show the X-ray irradiation period and the charge accumulation / readout in the high-definition imaging mode of the present modification corresponding to the periods of FIGS. 5A to 5C. The period, the high-definition projection data generation period, and the high-definition image data generation period are shown. However, FIG. 5 shows a case where each of the charge accumulation period and the charge readout period in the high-definition imaging mode is shortened to about 1/3 with respect to the charge accumulation period and the charge readout period in the standard imaging mode. In the imaging period Tx, charge accumulation and charge readout three times and charge reset once are performed. On the other hand, X-ray irradiation in the imaging period Tx is continuously performed in a period αb from time t10 when the first charge accumulation is started to time tb1 when the third charge accumulation is almost finished.

  That is, in the X-ray imaging in the high-definition imaging mode of this modification, based on preset X-ray irradiation conditions, the times t10, t20, t30,... As shown in FIG. X-ray irradiation in the irradiation period αb and the irradiation period Tb (Tb = Tx) is repeatedly performed by the high voltage generation unit 5 and the X-ray generation unit 2. At this time, for example, in the first imaging period Tx, signal charge accumulation in the periods [t10 to tb11], [tb12 to tb13], and [tb14 to tb15] in FIG. 5E and the periods [tb11 to tb12], Reading of signal charges in [tb13 to tb14] and [tb15 to tb16] and resetting (erasing) of signal charges in the period [tb16 to t20] are performed by the high-definition X-ray detection unit 3b.

  Then, the high-definition projection data generation unit 4b generates high-definition projection data based on the readout charges described above in the period γb with reference to the times tb12, tb14, and tb16 in FIG. ) In the period βb based on the time t20, the first high-definition projection data generated at the time tb12, the second high-definition projection data generated at the time tb14, and the third high-definition data generated at the time tb16. Generation of high-definition image data based on the fine projection data is performed by a high-definition image data generation unit 9bx described later.

  Note that the shortening rate of the charge accumulation period and the charge readout period in the high-definition imaging mode of this modification with respect to the standard imaging mode is not limited to 1/3. The shortening rate of the charge accumulation period and the shortening rate of the charge reading period may be different.

  Next, a specific configuration and function of the high-definition image data generation unit in this modification will be described with reference to the block diagram of FIG.

  The high-definition image data generation unit 9bx of this modification shown in FIG. 6 performs non-destructive readout of signal charges under X-ray irradiation performed continuously in the X-ray irradiation period αb shown in FIG. Using a CMOS image sensor or the like that can be performed at high speed as the high-definition X-ray detection unit 3b, the X-ray imaging in the high-definition imaging mode that is faster than the X-ray imaging in the standard imaging mode is performed a plurality of times in the imaging period Tx. It has a function of generating high-definition image data excellent in spatial resolution and sensitivity based on a plurality of high-definition projection data.

  In FIG. 6, the units of the high-definition image data generation unit 9bx having the same configuration and functions as the units of the high-definition image data generation unit 9b shown in FIG. Omitted.

  That is, the high-definition image data generation unit 9bx in the present modification includes a sub-image data generation unit 91x, an image data synthesis unit 92, and an image data processing unit 93 as shown in FIG. A projection data storage unit 911, a subtraction processing unit 912, and a sub image data storage unit 913 are provided.

  For example, the first high-definition projection data to the third high-definition projection data supplied from the high-definition projection data generation unit 4b of the X-ray imaging unit 1 at times tb12, tb14, and tb16 in FIG. The data is sequentially stored in the projection data storage unit 911 of the data generation unit 91x.

  Next, the subtraction processing unit 912 of the sub image data generation unit 91x performs the period [tb12 to tb13] as the X-ray irradiation period by the subtraction process between the second high definition projection data and the first high definition projection data. Second sub-image data equivalent to the sub-image data is generated, and similarly, the period [tb14 to tb15] is irradiated with X-rays by the subtraction process between the third high-definition projection data and the second high-definition projection data. Third sub image data equivalent to the sub image data in the period is generated. The first sub image data generated by using the second sub image data, the third sub image data, and the first high-definition projection data generated in the subtraction processing unit 912 as described above is sub image data. The data is temporarily stored in the sub image data storage unit 913 of the generation unit 91x.

  On the other hand, the positional deviation correction unit 921 of the image data composition unit 92 detects the positional deviation of the first to third sub-image data read from the sub-image data storage unit 913, and the obtained positional deviation detection. Based on the result, the positional deviation of each sub-image data is corrected. Then, the synthesis processing unit 922 of the image data synthesis unit 92 generates high-definition image data by adding and synthesizing the first sub-image data to the third sub-image data corrected for positional deviation.

  Next, the image data processing unit 93 performs image processing such as filtering processing on the high-definition image data supplied from the image data synthesizing unit 92 as necessary, and sends the processed high-definition image data to the display unit 10. Supply.

  According to the embodiment of the present disclosure and the modification thereof described above, when high-definition image data is generated using a high-definition X-ray detection unit with a fine pixel pitch, signals accumulated in the high-definition X-ray detection unit By increasing the charge readout speed, a plurality of sub-image data are collected in a predetermined shooting period, and positional sensitivity correction and addition synthesis are performed on these sub-image data to achieve good sensitivity and spatial resolution. High-definition image data can be collected.

  In particular, since the X-ray irradiation period per time is shortened, dynamic blur caused by the irradiation period is reduced. Also, by synthesizing the sub-image data collected using X-rays of such a short irradiation period, high-definition image data is collected using an X-ray dose that is substantially the same as when using a standard X-ray detector. This makes it possible to prevent S / N deterioration of the image data.

  Further, since the tube current per unit time is not increased, there is no need to select a large focal spot size in the X-ray tube, and deterioration of the spatial resolution can be prevented.

  On the other hand, according to the above-described modification, the above-described high-definition image data excellent in sensitivity and spatial resolution can be collected without using a high-speed pulse rate by using the non-destructive readout function provided in the high-definition X-ray detection unit. It becomes possible to do.

  As mentioned above, although embodiment of this indication and its modification were described, this indication is not limited to the above-mentioned embodiment and its modification, and it can change and carry out further. For example, in the above-described embodiment, the X-ray diagnostic apparatus applied to the examination of the circulatory region has been described. However, an X-ray diagnostic apparatus intended for examination of other areas such as the abdomen may be used.

  Further, in the above-described embodiment, the X-ray imaging in the high-definition imaging mode in which the charge accumulation period and the charge readout period are shortened to 1/2 with respect to the X-ray imaging in the standard imaging mode is described. Although the X-ray imaging in the high-definition imaging mode shortened to 3 has been described, the shortening rate is not limited to these values. Further, the shortening rate of the charge accumulation period and the shortening rate of the charge reading period may be different.

  Note that each unit included in the X-ray diagnostic apparatus 100 of the present embodiment can be realized by using, for example, a computer including a CPU, a RAM, a magnetic storage device, an input device, a display device, and the like as hardware. it can. For example, the system control unit 12 of the X-ray diagnostic apparatus 100 can realize various functions by causing a processor such as a CPU mounted on the computer to execute a predetermined control program. In this case, the above-described control program may be installed in advance in the computer, or may be stored in a computer-readable storage medium or installed in the computer of the control program distributed via the network. .

  Although several embodiments of the present invention have been described above, these embodiments are presented as examples 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 ... X-ray imaging part 2 ... X-ray generation part 3a ... X-ray detection part 3b ... High definition X-ray detection part 4a ... Standard projection data generation part 4b ... High definition projection data generation part 5 ... High voltage generation part 6 ... Holding Unit 7 ... Top plate 8 ... Movement mechanism unit 81 ... Detection unit movement mechanism 82 ... Holding unit movement mechanism 83 ... Top plate movement mechanism 84 ... Movement mechanism control unit 9a ... Standard image data generation units 9b, 9bx ... High-definition image data generation Unit 91 ... Sub image data generation unit 911 ... Projection data storage unit 912 ... Subtraction processing unit 913 ... Sub image data storage unit 92 ... Image data composition unit 921 ... Position shift correction unit 922 ... Composition processing unit 93 ... Image data processing unit 10 ... Display unit 11 ... Input unit 12 ... System control unit 100 ... X-ray diagnostic apparatus

Claims (9)

  1. When cormorants row X-ray imaging Te predetermined shooting period smell high-definition shooting mode to the subject, a high-definition projection data more performed multiple times and accumulated as charge in the charge reading in the predetermined shooting period Generating X-ray imaging means;
    Sub-image data generating means for generating a plurality of sub-image data for the predetermined imaging period based on each of the plurality of high-definition projection data;
    A positional deviation correction unit that detects a relative positional deviation of the plurality of sub-image data and corrects the positional deviation based on the detection results;
    Synthesis processing means for generating high-definition image data for one frame in the predetermined shooting period by adding and synthesizing the plurality of sub-image data corrected for positional deviation;
    An X-ray diagnostic apparatus comprising: display means for displaying the high-definition image data.
  2. The X-ray imaging means reads X-ray generation means for performing X-ray irradiation a plurality of times during the predetermined imaging period, and reads out signal charges accumulated in the X-ray detection element corresponding to each of the X-ray irradiations. High-definition X-ray detection means for detecting X-rays transmitted through the subject, and high-definition projection data generated based on the signal charges read by the high-definition X-ray detection means The X-ray diagnostic apparatus according to claim 1, further comprising projection data generation means.
  3. The X-ray imaging means includes X-ray generation means for performing X-ray irradiation once in the predetermined imaging period, and signal charges sequentially accumulated in the X-ray detection element during the X-ray irradiation period at a plurality of times. High-definition X-ray detection means for detecting X-rays transmitted through the subject by reading across the subject, and the plurality of high-definition projection data based on the signal charges read by the high-definition X-ray detection means The X-ray diagnostic apparatus according to claim 1, further comprising high-definition projection data generation means for generating.
  4.   4. The X-ray diagnostic apparatus according to claim 3, wherein the high-definition X-ray detection means performs nondestructive readout of signal charges sequentially accumulated in the X-ray detection element.
  5.   The X-ray diagnostic apparatus according to claim 2 or 3, wherein the high-definition X-ray detection means uses a CMOS image sensor as the X-ray detection element.
  6.   The sub-image data generation means performs a subtraction process on adjacent high-definition projection data in the high-definition projection data generated in time series by the X-ray imaging means, thereby performing the sub-image data The X-ray diagnostic apparatus according to claim 3, wherein:
  7.   Standard image data generation means for generating standard image data based on standard projection data generated by X-ray imaging in the standard imaging mode by the X-ray imaging means, and the high-definition X-ray detection means are moved to a desired position. 4. The X-ray detection apparatus according to claim 2, further comprising a moving unit, wherein the moving unit moves the high-definition X-ray detection unit with respect to a precision inspection region indicated in the standard image data. Line diagnostic equipment.
  8.   The X-ray diagnosis apparatus according to claim 1, wherein the misalignment correction unit detects misalignment between sub image data by applying pattern matching processing to the plurality of sub image data.
  9. For an X-ray diagnostic apparatus that generates high-definition image data based on high-definition projection data collected by X-ray imaging in a high-definition imaging mode for a subject,
    When Cormorant row Te the high resolution imaging mode X-ray imaging the predetermined shooting period smell, and the storage and the charge of the charge reading in the predetermined shooting period performed a plurality of times to generate a plurality of high-definition projection data X-ray imaging function,
    A sub-image data generation function for generating a plurality of sub-image data for the predetermined photographing period based on each of the plurality of high-definition projection data;
    A positional deviation correction function for detecting a relative positional deviation of the plurality of sub-image data and correcting the positional deviation based on the detection results;
    A synthesis processing function for generating high-definition image data for one frame in the predetermined shooting period by adding and synthesizing the plurality of sub-image data corrected for positional deviation;
    A control program for executing a display function for displaying the high-definition image data.
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