JP3623308B2 - X-ray diagnostic imaging equipment - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to an X-ray diagnostic imaging apparatus having a filter control device that controls insertion / retraction of an X-ray compensation filter using a fluoroscopic image, and particularly appropriately arranges the X-ray compensation filter according to X-ray imaging conditions. The present invention relates to an X-ray diagnostic imaging apparatus capable of obtaining a good X-ray fluoroscopic image.
[0002]
A conventional X-ray diagnostic imaging apparatus has a configuration disclosed in Japanese Patent Laid-Open No. 05-253213.
[0003]
Among the above-described configurations, the X-ray compensation filter control device is electrically connected to the television camera having the above-described configuration and stores the fluoroscopic image data output from the television camera, and the fluoroscopic image storage unit and the electric image storage unit. A phenomenon in which gradation is not discernible even if the fluoroscopic image data is read out from the fluoroscopic image storage unit and the fluoroscopic image data exhibits a high luminance pixel value and is displayed on the screen (referred to as “halation phenomenon”). A control amount calculating means for calculating a control amount for covering a pixel region having a pixel value (referred to as a “threshold value”) or higher with an X-ray compensation filter having the above-described configuration; and the control amount calculating means electrically connected to the control amount calculating means. The X-ray compensation filter based on the control amount inserts the X-ray compensation filter into a pixel region that is equal to or greater than a threshold value depending on the shape and position of the pixel region, and the pixel region that is less than the threshold value And a filter control unit for al retracted. Further, the threshold value is a condition for generating an imaging region of an object and X-rays, that is, a voltage of a power source (hereinafter referred to as “tube voltage”) and a current (hereinafter referred to as “tube current”) supplied to the X-ray generation unit having the above configuration. ) And X-ray irradiation time conditions (referred to as “X-ray imaging conditions”).
As described above, the X-ray compensation filter control apparatus inserts the X-ray compensation filter so as to cover an area equal to or greater than a preset threshold value.
In addition, when an X-ray compensation filter is already inserted based on a predetermined threshold value for certain fluoroscopic image data, the fluoroscopic image data on the fluoroscopic image data is based on the X-ray compensation filter position information currently arranged. X-ray compensation filter position is calculated, X-ray attenuation amount due to insertion of the X-ray compensation filter is stored, and fluoroscopic image data not covered by the X-ray compensation filter based on the attenuation amount And inserting the X-ray compensation filter so as to cover a pixel area equal to or higher than a preset threshold value in the fluoroscopic image data separate from the fluoroscopic image data, The X-ray compensation filter is retracted.
[0004]
[Problems to be solved by the invention]
Recently, in addition to conventional image diagnosis, interventional radiology in which a catheter is advanced to a lesion while treating the image while viewing the image has been actively performed. For this reason, there is a demand for moving the imaging position of the subject to follow the catheter, for example. Naturally, if the subject is moved, the thickness of transmission of the X-rays changes, and accordingly, the X-ray imaging conditions need to be changed. As described above, there is a problem in that the subject is not necessarily inserted so as to cover a pixel region (for example, a pixel region having the halation phenomenon) other than the pixel region in which the X-ray compensation filter is suitable for the diagnosis target.
[0005]
The present invention has been made to solve the above-described problems, and an object of the present invention is to cover a pixel region other than a pixel region suitable for an object to be diagnosed by following the change in the X-ray imaging condition of the X-ray compensation filter. It is an object of the present invention to provide an X-ray diagnostic imaging apparatus that controls insertion at such a position and thereby obtains a fluoroscopic image suitable for diagnosis.
[0006]
[Means for Solving the Problems]
The object is to provide an X-ray generator for generating X-rays, X-ray control means for controlling X-ray imaging conditions using the X-rays, and a member disposed on the side irradiated with the X-rays to attenuate the X-rays. An X-ray compensation filter formed from the image intensifier, an image intensifier arranged to face the X-ray generation unit with the subject interposed therebetween, and to receive the X-ray transmitted through the subject and convert it into an optical image, A television camera that is optically joined to an image intensifier and captures the optical image and outputs a fluoroscopic image; a fluoroscopic image storage means that is connected to the television camera and stores the fluoroscopic image; and the X-ray imaging conditions Correspondingly, a threshold value storage means for storing a pixel value at which the halation phenomenon of the X-ray fluoroscopic image occurs as a threshold value, and the fluoroscopic image storage means and the threshold value storage means are respectively connected to the transparent image. An X-ray compensation filter connected to the X-ray compensation filter and the insertion-area calculation unit, respectively, for inserting an image-reading area and calculating a pixel area equal to or greater than the threshold as an X-ray compensation filter insertion area; In the X-ray diagnostic imaging apparatus including filter control means for inserting the X-ray into the insertion area, the X-ray compensation filter is disposed in the insertion area of the first X-ray imaging condition, and the X-ray control means When a second X-ray imaging condition different from the X-ray imaging condition is set, the X-ray control unit is connected to the first X-ray imaging condition and is arranged corresponding to the first X-ray imaging condition. Attenuation amount calculation means for calculating the attenuation amount of the X-ray by the X-ray compensation filter, and X-ray fluoroscopy when the X-ray compensation filter is not inserted based on the attenuation amount connected to the attenuation amount calculation means Image conversion means for converting each pixel value of the image into a converted image, and the insertion area calculation means is connected to the image conversion means, and the threshold is determined from a threshold value corresponding to the X-ray imaging condition of the converted image. A pixel area greater than or equal to the value is calculated as an insertion area corresponding to the second X-ray imaging condition of the X-ray compensation filter, and the filter control means corresponds to the X-ray compensation filter corresponding to the second X-ray imaging condition. This is achieved by inserting into the inserted area.
[0007]
In addition, an X-ray generation unit that generates X-rays, an X-ray control unit that controls X-ray imaging conditions by the X-rays, and a member that is disposed on the side irradiated with the X-rays and attenuates the X-rays An X-ray compensation filter, an image intensifier arranged to face the X-ray generation unit with the subject interposed therebetween and receiving the X-ray transmitted through the subject and converting it into an optical image, A television camera that is optically joined to an intensifier and captures the optical image and outputs a fluoroscopic image; a fluoroscopic image storage means that is connected to the television camera and stores the fluoroscopic image; and corresponds to the X-ray imaging conditions. Threshold value storage means for storing a pixel value at which a halation phenomenon of the X-ray fluoroscopic image occurs as a threshold value, and the fluoroscopic image storage means and the threshold value storage means connected to the fluoroscopic image, respectively. Insertion area calculation means for reading out and calculating a pixel area equal to or greater than the threshold value as an insertion area for the X-ray compensation filter; and the X-ray compensation filter connected to the X-ray compensation filter and the insertion area calculation means, respectively. In an X-ray diagnostic imaging apparatus including filter control means for inserting into an insertion area, the X-ray compensation filter is disposed in an insertion area for a first X-ray imaging condition, and the X-ray control means is configured to perform the first X-ray imaging. When set to a second X-ray imaging condition that is different from the conditions, the X is connected to the X-ray control means and arranged corresponding to the first X-ray imaging condition of the second X-ray imaging condition Attenuation amount storage means for calculating and storing the attenuation amount of the X-ray by the line compensation filter in advance, and X when the X-ray compensation filter is not inserted based on the attenuation amount connected to the attenuation amount storage means Image conversion means for converting each pixel value of the fluoroscopic image into a converted image, and the insertion area calculation means is connected to the image conversion means, and the threshold value corresponding to the X-ray imaging condition of the converted image is calculated from the threshold value. A pixel area equal to or greater than a threshold value is calculated as an insertion area corresponding to the second X-ray imaging condition of the X-ray compensation filter, and the filter control means sets the X-ray compensation filter as the second X-ray imaging condition. This is achieved by inserting into the corresponding insertion area.
[0008]
DETAILED DESCRIPTION OF THE INVENTION
Embodiments of the X-ray image diagnostic apparatus of the present invention will be described with reference to the drawings.
[0009]
First, a first embodiment will be described with reference to FIGS.
FIG. 1 is a block diagram showing a configuration example of the first embodiment of the X-ray image diagnostic apparatus of the present invention, FIG. 2 is a structural diagram showing a configuration example of the X-ray compensation filter of FIG. 1, and FIG. FIG. 4 is a graph showing a curve indicating the characteristics of tube voltage and X-ray energy absorption (relative value), and FIG. 4 is a display example of images before and after the X-ray compensation filter 4 of FIG. 2 moves on a fluoroscopic image. FIG.
[0010]
The X-ray diagnostic imaging apparatus according to the first embodiment includes a bed 2, an X-ray generation unit 3, an X-ray compensation filter 4, an image intensifier (hereinafter referred to as “II”) 5, a television camera 6, Image display processing unit 7, display output unit 8, fluoroscopic image storage unit 9, insertion position calculation unit 10, filter control unit 11, attenuation rate storage unit 12, attenuation amount calculation unit 13, X-ray generation control unit 14, and high pressure generation unit 15, an input operation unit 16, and a central processing unit 17.
The bed 2 carries the subject 1 and supports the subject 1 at an appropriate height from the floor surface. The X-ray generator 3 generates X-rays. The X-ray compensation filter 4 is disposed between the subject 1 and the X-ray generation unit 3 on the side where the X-ray is generated and irradiated, and attenuates the X-ray. I. I. Reference numeral 5 denotes an X-ray which is disposed opposite to the X-ray generator 3 with the subject 1 interposed therebetween and transmitted through the subject 1 is input to the fluorescent screen and converted into an optical image. The TV camera 6 is an I.D. I. 5 is optically joined to the optical image and converted into an electrical signal. The image display processing unit 7 is electrically connected to the television camera 6 and converts the electric signal into gradation data and outputs it. The display output unit 8 is electrically connected to the image display processing unit 7 to display and output the gradation data. The fluoroscopic image storage unit 9 is electrically connected to the television camera 6 and stores the electrical signal as fluoroscopic image data. The insertion region calculation unit 10 is electrically connected to the perspective image storage unit 9 and reads the perspective image data to calculate a pixel region equal to or greater than a preset threshold value. The filter control unit 11 is electrically connected to the insertion region calculation unit 10 and inserts the X-ray compensation filter 4 into the pixel region above the threshold value depending on the shape and position of the pixel region. Evacuate. Since the attenuation rate storage unit 12 calculates the filter insertion region by the insertion region calculation unit 10, attenuation rate data ρ indicating how much X-ray attenuation members such as aluminum and copper forming the X-ray compensation filter attenuate X-rays. I remember it. The attenuation amount calculation unit 13 is electrically connected to the attenuation rate storage unit 12 and the X-ray generation control unit 14, respectively. The attenuation rate data ρ and the X-ray imaging condition E (also referred to as “X-ray energy”) represented by the following equation. )) To calculate the attenuation amount F of the X-ray compensation filter.
E = kVnit (Formula 1)
E: X-ray energy, k: constant, V: tube voltage [kV], i: tube current [mA]
t: X-ray irradiation time [second], n: power multiplier related to tube voltage (2 ≦ n ≦ 5)
(Excerpted from the Japanese Radiologists Association, “Revised Supplemental Medical Radiation Data Book”, published in September 1984, Magblos Publishing, page 32.)
F = ρE (in the case of linear attenuation) (Expression 2)
The X-ray generation control unit 14 is electrically connected to the high-voltage generation unit 15 and controls X-ray imaging conditions such as tube voltage, tube current, and X-ray irradiation time applied to the X-ray generation unit 3. The high voltage generation unit 15 is electrically connected to the X-ray generation unit 3 and supplies the X-ray generation unit 3 with an amount of electric power based on the X-ray imaging conditions. The input operation unit 16 allows the central processing unit 17 and the operator to input various information such as X-ray imaging conditions. The central controller 15 includes the X-ray compensation filter 4, I.I. I. 5, TV camera 6, image display processing unit 7, perspective image storage unit 9, insertion region calculation unit 10, filter control unit 11, attenuation amount storage unit 12, attenuation amount calculation unit 13, and X-ray generation control unit 14 They are electrically connected and controlled based on the information.
[0011]
In addition, as shown in FIG. 2, the X-ray compensation filter 4 includes four parts including a U part located at the top of the drawing, a D part located below, an L part located on the left side, and an R part located on the right side. The blades U, D, L, and R are each moved in parallel by moving back and forth or left and right around the display area of the fluoroscopic image indicated by the circle in the drawing, or by rotating and moving the four pieces. The size of the opening formed by the blades is adjusted.
[0012]
In addition, as shown in (Equation 1), the tube voltage and the relative value of the X-ray energy absorption (I.I.5 are typical materials for fluorescent screens) that have the greatest influence on the X-ray imaging conditions. When the tube voltage of cesium iodide (chemical formula: CsI), particularly when a human body or the like is used as a subject, only a portion of 40 to 120 [kV] is extracted, the characteristic is represented by a dotted line in FIG. When the case of passing through an X-ray compensation filter with an attenuation ratio ρ is measured by the same method, if expressed using ρ, the characteristic shown by the dotted line is multiplied by 1-ρ, and the characteristic shown in FIG. The inventor verified that it is represented by a solid line.
[0013]
Next, the operation of the X-ray image diagnostic apparatus according to the first embodiment will be described.
X-rays irradiated to the subject 1 from the X-ray generation unit 3 through the X-ray compensation filter 4 pass through the subject 1 and pass through the subject 1. I. 5 is converted into an optical image. The optical image is captured by the television camera 6 and stored in the perspective image storage unit 9. The insertion region calculation unit 10 calculates a pixel region that covers a pixel region that is equal to or greater than a preset threshold value with the X-ray compensation filter 4. The filter control unit 11 inserts the X-ray compensation filter 4 in the pixel area above the threshold value according to the shape and position of the pixel area, and retracts it from the pixel area below the threshold value.
Here, in order to explain more specifically, the case where the X-ray compensation filter 4 is inserted as shown in FIG. 4 (b) from the case where it is inserted as shown in FIG. 4 (a). An example of moving to Here, in order to simplify the description, one of the blades of each of U, D, L, and R is used.
First, the central processing unit 17 detects the insertion position of the X-ray compensation filter 4 on the fluoroscopic image data when the X-ray compensation filter 4 is arranged at a position corresponding to FIG. Under such X-ray compensation filter arrangement conditions, for example, the tube voltage is 70 kV, the tube current and the X-ray irradiation time are constant (the same applies to the following imaging), and fluoroscopic image data is obtained under the X-ray imaging conditions. . The image data is displayed and output to the display output unit 9 through the image display processing unit 8 as shown in FIG.
Next, since the subject moves and becomes thicker to transmit X-rays, sufficient transmission X-rays cannot be obtained under the X-ray generation condition of tube voltage 70 [kV]. For example, tube voltage 80 [kV] ] Is adjusted by increasing the X-ray imaging conditions. Further, as shown in FIG. 3, if the tube voltage is increased, the amount of X-ray absorption is reduced, and the same can be said for the vane-type attenuation member constituting the X-ray compensation filter. Under the radiographic conditions, the halation phenomenon has not occurred before, so that the X-ray compensation filter 4 under the X-ray radiographing conditions is set to the threshold value in order to properly display the pixel area below the threshold value. It is necessary to insert the X-ray compensation filter 4 to the above pixel region, that is, to narrow the opening formed by the X-ray compensation filter 4 from the current position.
Therefore, when the thickness of the subject is increased, the X-ray attenuation due to insertion of the X-ray compensation filter 4 is read, and the attenuation rate by the attenuation member of the X-ray compensation filter stored from the attenuation rate storage unit 12 is read. Using the attenuation amount calculated by the attenuation amount calculation unit 13, the fluoroscopic image data when there is no X-ray compensation filter 4 is calculated. The insertion position calculation unit 10 calculates the position of the X-ray compensation filter 4 based on a preset threshold value under a new X-ray imaging condition 80 [kV] using the fluoroscopic image data and the current The movement amount of the blade is calculated from the difference from the position. The filter control unit 11 moves the X-ray compensation filter 4 based on the amount of movement to narrow the opening. Under such X-ray compensation filter arrangement conditions, fluoroscopic image data is obtained under X-ray imaging conditions with a tube voltage of 80 [kV]. The image data is displayed and output to the display output unit 9 through the image display processing unit 8 as shown in FIG.
Further, the thickness of the X-ray transmission through the subject is reduced, and the X-ray generation condition of the tube voltage of 70 [kV] is not suitable in terms of the X-ray exposure dose given to the subject. For example, the X-ray imaging conditions are lowered and adjusted to a tube voltage of 60 [kV]. Also, as shown in FIG. 3, if the tube voltage is lowered, the amount of X-ray absorption increases, and the same can be said for the vane-type attenuation member constituting the X-ray compensation filter. The X-ray imaging may be used to display a pixel region below the threshold value without interposing the X-ray compensation filter. Under certain conditions, the X-ray compensation filter 4 needs to be retracted to a pixel area equal to or greater than a threshold value, that is, the opening needs to be expanded from the current position. In this case, the difference is only whether the opening is narrowed or widened, and the description thereof is omitted.
[0014]
Since the X-ray diagnostic imaging apparatus according to the first embodiment is configured as described above, the pixels other than the pixel region adapted to the diagnosis target by tracking the X-ray compensation filter 4 according to changes in the X-ray imaging conditions. Insertion control can be performed at a position covering the area.
[0015]
Next, a second embodiment will be described with reference to FIGS.
2 to 4 have been described in the embodiment of the first invention, the description thereof will be omitted. FIG. 5 is a block diagram showing a configuration example of the second embodiment of the X-ray diagnostic imaging apparatus of the present invention.
[0016]
The X-ray diagnostic imaging apparatus according to the second embodiment includes a bed 2, an X-ray generator 3, an X-ray compensation filter 4, an I.D. I. 5, TV camera 6, image display processing unit 7, display output unit 8, fluoroscopic image storage unit 9, insertion position calculation unit 10, filter control unit 11, attenuation amount conversion storage unit 18, X-ray generation control unit 14, and high pressure generation A unit 15, an input operation unit 16, and a central processing unit 17.
A bed 2, an X-ray generator 3, an X-ray compensation filter 4, and an I.S. I. 5, TV camera 6, image display processing unit 7, display output unit 8, fluoroscopic image storage unit 9, insertion position calculation unit 10, filter control unit 11, X-ray generation control unit 14, high pressure generation unit 15, and input operation unit 16. Since it was explained in the embodiment of the first invention, its explanation is omitted. The attenuation amount conversion storage unit 18 has the functions of the attenuation rate storage unit 12 and the attenuation amount calculation unit 13, and is electrically connected to the insertion position calculation unit 11 and the X-ray generation control unit 14. Therefore, the attenuation amount F of the X-ray compensation filter is calculated in advance from the attenuation rate data ρ indicating how much the X-ray attenuation member such as aluminum or copper forming the X-ray compensation filter attenuates. It is converted from (Expression 1) and (Expression 2) and stored. The central controller 15 includes the X-ray compensation filter 4, I.I. I. 5, the TV camera 6, the image display processing unit 7, the fluoroscopic image storage unit 9, the filter insertion area calculation unit 10, the filter control unit 11, the attenuation amount conversion storage unit 18, and the X-ray generation control unit 14 are electrically connected to each other. Each is controlled based on the information.
[0017]
Next, the operation of the X-ray image diagnostic apparatus according to the second embodiment will be described.
First, the display output of the X-ray fluoroscopic image in the X-ray compensation filter at the position corresponding to FIG. 4A is the same as that in the first embodiment, and thus the description thereof is omitted.
Next, the thickness of the X-ray compensation filter stored in the attenuation amount conversion storage unit 18 is reduced by the X-ray attenuation due to the insertion of the X-ray compensation filter 4 by increasing the thickness through which the subject moves and transmits X-rays. The amount of attenuation by the member is read, and the fluoroscopic image data when the calculation unit included in the central processing unit 17 or the image display processing unit 8 does not have the X-ray compensation filter 4 is calculated. The insertion position calculation unit 10 calculates the position of the X-ray compensation filter 4 based on a preset threshold value under a new X-ray imaging condition 80 [kV] using the fluoroscopic image data and the current The amount of movement of each part of the blades U, D, L, R is calculated from the difference from the position. The filter control unit 11 moves the X-ray compensation filter 4 based on the movement amount calculated for each blade to narrow the opening. Under such X-ray compensation filter arrangement conditions, fluoroscopic image data is obtained under X-ray imaging conditions with a tube voltage of 80 [kV]. The image data is displayed and output to the display output unit 9 through the image display processing unit 8 as shown in FIG.
[0018]
Since the X-ray diagnostic imaging apparatus according to the second embodiment is configured as described above, the pixels other than the pixel region adapted to the diagnosis target by tracking the X-ray compensation filter 4 according to changes in the X-ray imaging conditions. Insertion control can be performed at a position that covers the region, and calculation by the attenuation amount calculation unit described in the first embodiment is unnecessary, so that changes in X-ray imaging conditions can be followed more quickly. In addition, since only the attenuation amount conversion storage unit is required instead of the attenuation rate storage unit and the attenuation amount calculation unit, it is possible to follow changes in X-ray imaging conditions with a simpler structure.
[0019]
In addition, as an X-ray image diagnostic apparatus according to the third embodiment, control is performed in which the blades constituting the X compensation filter described in FIG. 2 are multiplexed in the X-ray irradiation direction to follow changes in X-ray imaging conditions. May be. FIG. 6 shows a configuration diagram of an X-ray compensation filter having two blades. Each of these two blades has a pixel area where halation occurs, and a pixel area where halation does not occur but when the tube voltage is boosted, the halation occurs immediately (hereinafter, the pixel where halation is likely to occur). Use them to cover each area). For example, two blades are inserted in a pixel region where halation is occurring, and one of the two blades is inserted in a pixel region where halation is likely to occur. For example, U, D, L, and R blades are made of a material having a relatively low X-ray absorption rate, and U1, D1, L1, and R1 are made of a material having a high absorption rate. That is, only an X-ray compensation filter composed of U, D, L, and R is inserted into a pixel region where halation is likely to occur, and U1, D1, L1, and R1 are inserted into the pixel region where halation is occurring. insert. Further, when the tube voltage is further increased, U and U1, D and D1, L and L1, and R and R1 may be inserted in an overlapping manner.
[0020]
Since the X-ray image diagnostic apparatus according to the third embodiment is configured as described above, the pixels other than the pixel region adapted to the diagnosis target by tracking the X-ray compensation filter 4 in accordance with changes in the X-ray imaging conditions. Insertion control can be performed at a position that covers the region, and changes in X-ray imaging conditions can be finely followed by a plurality of blades, as compared with the first and second embodiments.
[0021]
Regardless of how the above-described embodiments are combined, the X-ray compensation filter 4 can be inserted and controlled at a position covering a pixel area other than the pixel area suitable for the diagnosis target following the change in the X-ray imaging conditions. Needless to say.
[0022]
【The invention's effect】
The present invention provides the X-ray attenuation amount when the X-ray compensation filter is inserted at the insertion position of the X-ray compensation filter based on the X-ray imaging condition arbitrarily changed by the X-ray attenuation amount calculation means. The X-ray compensation filter insertion region calculation means calculates the pixel region based on the attenuation amount, and the X-ray compensation filter control means calculates the X-ray compensation filter by the pixel region based on the attenuation amount. Since insertion or retraction is performed, the X-ray compensation filter can be controlled to follow the change in X-ray imaging conditions and cover a pixel area other than the pixel area suitable for the diagnosis target. There is an effect that an X-ray image diagnostic apparatus which is an appropriate position and can obtain an X-ray fluoroscopic image suitable for diagnosis can be provided.
[Brief description of the drawings]
FIG. 1 is a block diagram showing a configuration example of a first embodiment of an X-ray image diagnostic apparatus according to the present invention.
FIG. 2 is a structural diagram showing a configuration example of the X-ray compensation filter of FIG. 1;
FIG. 3 is a graph showing a curve indicating the characteristics of tube voltage and X-ray energy absorption (relative value) among X-ray imaging conditions.
4 is a diagram showing a display example of an image before and after the X-ray compensation filter 4 of FIG. 2 moves on a fluoroscopic image.
FIG. 5 is a block diagram showing a configuration example of a second embodiment of the X-ray image diagnostic apparatus of the present invention.
FIG. 6 is a configuration diagram of an X-ray compensation filter having two blades each.
[Explanation of symbols]
11 Filter Control Unit 12 Attenuation Rate Storage Unit 13 Attenuation Amount Calculation Unit 18 Attenuation Amount Conversion Storage Unit

Claims (1)

An X-ray generator for generating X-rays;
X-ray control means for controlling the energy of X-rays generated by the X-ray generator,
Threshold storage means for storing, as a threshold value, a pixel value at which the halation phenomenon of the fluoroscopic image occurs corresponding to the X-ray energy controlled by the X-ray control means;
An X-ray compensation filter formed from a member that is disposed on the X-ray generation side of the X-ray generation unit and attenuates the X-ray;
An image intensifier that is disposed opposite to the X-ray generation unit with the subject interposed therebetween and receives the X-ray transmitted through the subject and converts it into an optical image, and the image intensifier converted by the image intensifier A television camera that captures optical images and outputs perspective images;
An insertion area calculating means for calculating a fluoroscopic image output by the television camera as a pixel area equal to or greater than a threshold stored in the threshold storage means as an insertion area of the X-ray compensation filter;
Filter control means for inserting the X-ray compensation filter into the insertion area calculated by the insertion area calculation means;
In an X-ray diagnostic imaging apparatus comprising: an attenuation rate storage unit that stores an attenuation rate of the X-ray compensation filter measured with a predetermined X-ray energy; an attenuation rate stored in the attenuation rate storage unit; and a attenuation amount calculating means from a controlled X-ray energy by the X-ray control means for calculating the attenuation of the X-ray compensation filter, said filter control means based on the attenuation amount calculated by the attenuation amount calculation section the An X-ray image diagnostic apparatus characterized by controlling an X-ray compensation filter.

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