JPH09262227A - X-ray image diagnostic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an X-ray diagnostic apparatus to obtain an adequate X-ray perspective by putting an X-ray compensation filter on to the most appropriate parts through the operation to compensate X-ray attenuation due to the filter by fluoroscopy condition. SOLUTION: A perspective is obtained on the condition that, for example, the tube voltage is 70kv given that the X-ray exposure time is fixed to set the X-ray compensation filter. The voltage is raised up to 80kv incidentally to obtain sufficient X-ray transmission when the subject moves and exposes its more thick part. Factor of the X-ray attenuation caused by putting an X-ray compensation filter 4 is read out from a attenuation factor memory 12 to operate the perspective data in the case that the filter 4 is not put applying the attenuation factor operated in an attenuation factor operation sector 13. An insert location calculation sector 10 is to calculate the position of the filter 4 as well as its move distance comparing to actual location based on the preset threshold prepared for new fluoroscopy condition applying the perspective data so as to move the filter 4.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray image diagnostic apparatus having a filter control device for inserting / withdrawing control of an X-ray compensation filter using a fluoroscopic image, and particularly to X-ray compensation according to X-ray imaging conditions. The present invention relates to an X-ray image diagnostic apparatus capable of properly arranging filters to obtain a favorable X-ray fluoroscopic image.

A conventional X-ray image diagnostic apparatus has a configuration disclosed in Japanese Patent Laid-Open No. 05-253213.

In the above-mentioned configuration, the X-ray compensation filter control device is electrically connected to the television camera having the above-mentioned configuration and stores a perspective image storage unit for storing perspective image data output from the television camera, and the perspective image storage. Phenomenon in which gradations cannot be identified even when the fluoroscopic image data is read out from the fluoroscopic image storage unit by being electrically connected to the image display unit and the fluoroscopic image data has a high pixel value in terms of luminance and is displayed on the screen (“halation phenomenon”). Control amount calculation means for calculating a control amount for covering a pixel region having a pixel value (referred to as "threshold value") or more, which is referred to as "threshold value", by the X-ray compensation filter having the above-described configuration, and the control amount calculation means electrically. The connected X-ray compensation filter based on the control amount inserts the X-ray compensation filter into a pixel region having a threshold value or more depending on the shape and position of the pixel region, and And a filter control unit for retracting from the pixel region. Further, the threshold value is a condition (hereinafter referred to as "tube voltage") and current (hereinafter referred to as "tube current") of a power supply supplied to the X-ray generation unit having the above-mentioned configuration, that is, an imaging region of the subject and X-ray generation. ) And X-ray irradiation time conditions (referred to as “X-ray imaging conditions”). In this way, the X-ray compensation filter control device inserts the X-ray compensation filter so as to cover the area above the preset threshold value. When an X-ray compensation filter is already inserted based on a threshold value set in advance in certain fluoroscopic image data, the X-ray compensation filter on the fluoroscopic image data is used based on the currently arranged X-ray compensation filter position information. The X-ray compensation filter position is calculated, the attenuation amount of X-rays due to the insertion of the X-ray compensation filter is stored, and the fluoroscopic image data not covered by the X-ray compensation filter based on the attenuation amount. The X-ray compensation filter is inserted so as to cover a pixel area equal to or larger than a preset threshold value in the fluoroscopic image data different from the fluoroscopic image data, and the X-ray compensation filter is inserted from the pixel area less than the threshold value. The X-ray compensation filter is retracted.

[0004]

Recently, in addition to conventional image diagnosis, interventional radiology has been actively performed in which a catheter is advanced to a lesion while treating the image to treat the image. For this reason, there is a demand for moving the imaging position of the subject, for example, so as to follow the catheter. As a matter of course, if the subject is moved, the thickness of the X-ray transmitted therethrough changes, and the X-ray imaging conditions also need to change accordingly. 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 where the X-ray compensation filter is suitable for the diagnosis target.

The present invention has been made to solve the above problems, and an object thereof is to provide an X-ray compensation filter with an X-ray compensation filter.
Provided is an X-ray image diagnostic apparatus capable of tracking a change in radiographic conditions and controlling insertion at a position that covers a pixel region other than a pixel region suitable for a diagnosis target, thereby obtaining an X-ray fluoroscopic image suitable for diagnosis. Especially.

[0006]

The above-mentioned object is to provide an X-ray generation unit for generating X-rays, an X-ray control unit for controlling X-ray imaging conditions by the X-rays, and a side on which the X-rays are irradiated. An X-ray compensation filter that is arranged and formed of a member that attenuates the X-rays, and the X-rays that are arranged to face the X-ray generation unit with the subject in between and that have passed through the subject are converted into an optical image. Image intensifier, a television camera optically joined to the image intensifier, which captures the optical image and outputs a perspective image, and a perspective image memory which is connected to the television camera and stores the perspective image Means, threshold value storage means for storing, as a threshold value, a pixel value in which the halation phenomenon of the X-ray fluoroscopic image occurs corresponding to the X-ray imaging condition, the fluoroscopic image storage means, and the threshold value storage Insertion region calculation means connected to each of the stages and calculating the pixel region equal to or more than the threshold value as the insertion region of the X-ray compensation filter by reading the perspective image, the X-ray compensation filter and the insertion region calculation means, respectively. In an X-ray image diagnostic apparatus, which is connected and includes filter control means for inserting the X-ray compensation filter into the insertion area, the X-ray compensation filter is arranged in an insertion area of a first X-ray imaging condition, and the X-ray control is performed. Means is the first X
When the second X-ray imaging condition different from the X-ray imaging condition is set, it 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 calculation means for calculating the attenuation amount of the X-rays by the X-ray compensation filter, and each of the X-ray fluoroscopic images when the X-ray compensation filter is not inserted based on the attenuation amount connected to the attenuation amount calculation means. An image conversion means for converting the pixel value into a converted image is provided, and the insertion area calculation means is also connected to the image conversion means, and the threshold value corresponding to the X-ray imaging condition of the converted image is equal to or more than the threshold value. The pixel area is the X
By calculating as an insertion area corresponding to the second X-ray imaging condition of the line compensation filter, the filter control means inserts the X-ray compensation filter into the insertion area corresponding to the second X-ray imaging condition. To be achieved.

Further, an X-ray generator for generating X-rays, an X-ray control means for controlling the X-ray photographing condition by the X-rays, and an X-ray that is arranged on the side where the X-rays are irradiated are attenuated. An X-ray compensation filter formed of a member, an image intensifier that is arranged to face the X-ray generation unit with the subject in between, and receives the X-rays that have passed through the subject and converts the image into an optical image, A television camera optically joined to the image intensifier to capture the optical image and output a perspective image, a perspective image storage unit connected to the television camera to store the perspective image, and the X-ray imaging condition. Corresponding to the threshold value storage means for storing the pixel value causing the halation phenomenon of the X-ray fluoroscopic image as a threshold value, and the fluoroscopic image storage means and the threshold value storage means are respectively connected. The X-ray is connected to the insertion area calculation unit that reads out the transparent image and calculates a pixel area equal to or more than the threshold value as the insertion area of the X-ray compensation filter, and the X-ray compensation filter and the insertion area calculation unit. In an X-ray image diagnostic apparatus including a filter control unit that inserts a compensation filter into the insertion region, the X-ray compensation filter is arranged in an insertion region of a first X-ray imaging condition, and the X-ray control unit includes the first X-ray control unit. Second different from the X-ray imaging conditions
When the X-ray imaging condition is set to, the X-ray compensation filter is connected to the X-ray control means and is arranged corresponding to the first X-ray imaging condition of the second X-ray imaging condition. Attenuation amount storage means for preliminarily calculating and storing the attenuation amount of X-rays, and each pixel value of the X-ray fluoroscopic image when the attenuation amount storage means is connected and the X-ray compensation filter is not inserted based on the attenuation amount. An image conversion means for converting the converted image into a converted image is provided, and the insertion area calculation means is also connected to the image conversion means, and a pixel area equal to or more than the threshold value from a threshold value corresponding to an X-ray imaging condition of the converted image is converted. The X-ray compensation filter is calculated as an insertion area corresponding to the second X-ray imaging condition, and the filter control unit inserts the X-ray compensation filter into the insertion area corresponding to the second X-ray imaging condition. Achieved by That.

[0008]

BEST MODE FOR CARRYING OUT THE INVENTION Embodiments of an X-ray image diagnostic apparatus of the present invention will be described with reference to the drawings.

First, the first embodiment will be described with reference to FIGS.
This will be described with reference to FIG. 1 is a block diagram showing a configuration example of a first embodiment of an X-ray image diagnostic apparatus of the present invention, FIG.
3 is a structural diagram showing a configuration example of the X-ray compensation filter of FIG.
Is a graph showing a curve showing the characteristics of tube voltage and X-ray energy absorption (relative value) in the X-ray imaging conditions, and FIG. 4 shows before and after the X-ray compensation filter 4 of FIG. It is a figure which shows the example of a display of an image.

The X-ray image diagnostic apparatus of the first embodiment is
Bed 2, X-ray generation unit 3, X-ray compensation filter 4, image intensifier (hereinafter referred to as "II") 5, television camera 6, image display processing unit 7, display output unit 8, and perspective image storage. It includes a unit 9, an insertion position calculation unit 10, a filter control unit 11, an attenuation rate storage unit 12, an attenuation amount calculation unit 13, an X-ray generation control unit 14, a high voltage generation unit 15, an input operation unit 16, and a central processing unit 17. are doing. The bed 2 carries the subject 1 and supports the subject 1 at an appropriate height from the floor surface. The X-ray generation unit 3 generates X-rays. The X-ray compensation filter 4 uses the X
The X-ray is attenuated by being arranged between the subject 1 and the X-ray generator 3 on the side where the X-ray is generated and irradiated. I. I. Reference numeral 5 denotes a subject 1 which is arranged so as to face the X-ray generator 3 with the subject 1 interposed therebetween.
The X-rays that have passed through are input to the fluorescent screen and converted into an optical image for output. The TV camera 6 is an I.D. I. The optical image is inputted to the optical signal 5 and the optical image is inputted and converted into an electric signal and outputted. 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 electric signal as fluoroscopic image data. The insertion area calculation unit 10 is electrically connected to the fluoroscopic image storage unit 9 and reads the fluoroscopic image data to calculate a pixel area equal to or larger 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 a pixel region equal to or larger than 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 area by the insertion area calculation unit 10, 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 the X-rays is calculated. I remember. The attenuation amount calculation unit 13 is the attenuation rate storage unit 1
2 and the X-ray generation controller 14 are electrically connected to each other and the attenuation rate data ρ and the X-ray imaging condition E represented by the following equation
(Also referred to as "X-ray energy"), the attenuation amount F of the X-ray compensation filter is calculated. E = kVnit (Equation 1) E: X-ray energy, k: constant, V: tube voltage [kV],
i: tube current [mA] t: X-ray irradiation time [second], n: power factor related to tube voltage (2 ≦ n ≦ 5) (edited by Japan Radiological Society, “Revised and expanded medical radiation data book”, 1984) Published September, Magblos Publishing, 3rd
Excerpt from page 2. ) F = ρE (in the case of linear attenuation) (Equation 2) The X-ray generation control unit 14 is electrically connected to the high-voltage generation unit 15, and the tube voltage, the tube current, and the X-ray irradiation time given to the X-ray generation unit 3. X-ray imaging conditions such as. 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 to operate it. 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 controls the X-ray compensation filter 4, I.V. I. 5, TV camera 6, image display processing unit 7, perspective image storage unit 9, insertion area calculation unit 10, filter control unit 11, attenuation amount storage unit 12, attenuation amount calculation unit 13, X
It is electrically connected to each of the line generation control units 14 and controls each of them based on the above information.

As shown in FIG. 2, the X-ray compensation filter 4 has a U portion at the upper portion of the drawing and a D portion at the lower portion thereof.
Section, an L section located on the left side, and an R section located on the right side. Each of the blades U, D, L, and R is a display area of a perspective image indicated by a circle in the drawing. Centered on
Move it back and forth or left and right in parallel, or rotate it
The size of the opening formed by the blades is adjusted.

Further, as shown in (Equation 1), the characteristics of the relative value of the tube voltage and the energy absorption of X-rays, which have the greatest influence under the X-ray imaging conditions (typical of the phosphor screen of I.I.5). The tube voltage of cesium iodide (chemical formula: CsI), which is the material, is 40 to 40, especially when the human body is the subject.
If only the portion of 120 [kV] is extracted, the characteristic shown by the dotted line in FIG. 3 is obtained. When the case of passing through the X-ray compensation filter with the attenuation rate ρ is measured by the same method as described above, when expressed using ρ, the characteristic indicated by the dotted line is almost multiplied by 1-ρ, and The inventor verified that it is represented by a solid line.

Next, the operation of the X-ray image diagnostic apparatus according to the first embodiment will be described. The X-rays emitted from the X-ray generation unit 3 to the subject 1 through the X-ray compensation filter 4 pass through the subject 1 and are I.D. I. At 5, it is converted to an optical image. The optical image is captured by the television camera 6 and stored in the perspective image storage unit 9. The insertion area calculation unit 10 calculates a pixel area equal to or larger than a preset threshold value as a pixel area for covering with the X-ray compensation filter 4. The filter control unit 11 inserts the X-ray compensation filter 4 in a pixel region equal to or larger than the threshold value and withdraws it from the pixel region smaller than the threshold value, depending on the shape and position of the pixel region. Here, in order to explain more specifically, the X-ray compensation filter 4 is shown in FIG.
FIG. 4 from the case of being inserted as shown in FIG.
An example of moving to the case where it is inserted as shown in (b) is illustrated. Here, for simplicity,
One of the U, D, L, and R blades 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 current position information in which the X-ray compensation filter 4 is arranged at the position corresponding to FIG.
Under such an arrangement condition of the X-ray compensation filter, 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 the fluoroscopic image data is obtained. . 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, the thickness of the X-ray that is transmitted by the subject is increased and the X-ray generation condition of the tube voltage of 70 [kV] makes it impossible to obtain sufficient transmitted X-rays.
The adjustment is performed by raising the X-ray imaging condition to V].
Further, as shown in FIG. 3, when 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 that constitutes the X-ray compensation filter. Under the X-ray imaging condition, the halation phenomenon does not occur before. Therefore, in order to properly display the pixel area below the threshold value, the X-ray compensation filter 4 under the X-ray imaging condition is set to the threshold value. X to the above pixel area
It is necessary to insert the line compensation filter 4, that is, to narrow the opening formed by the X-ray compensation filter 4 from the current position. Therefore, when the subject becomes thicker, the X-ray attenuation amount due to the insertion of the X-ray compensation filter 4 and the attenuation rate by the attenuation member of the X-ray compensation filter stored in the attenuation rate storage unit 12 are read out, Using the attenuation amount calculated by the attenuation amount calculation unit 13, the fluoroscopic image data when the X-ray compensation filter 4 is not provided is calculated. The insertion position calculation unit 10 uses the fluoroscopic image data to calculate the position of the X-ray compensation filter 4 based on a preset threshold value under a new X-ray imaging condition 80 [kV], and The moving 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 movement amount to narrow the opening. Under such arrangement condition of the X-ray compensation filter, the fluoroscopic image data is obtained under the X-ray imaging condition of the 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. In addition, when the subject moves and the thickness of the X-ray is reduced, the tube voltage is 70 [kV], and the X-ray generation condition is as follows.
Since it is not appropriate in terms of the X-ray exposure dose given to the subject, the X-ray imaging condition is adjusted to a tube voltage of 60 [kV], for example. Further, as shown in FIG. 3, when the tube voltage is lowered, the amount of X-ray absorption increases, and the same can be said for the vane-shaped attenuation member that constitutes the X-ray compensation filter. Under
The area where the halation phenomenon does not occur may be covered with the X-ray compensation filter. Therefore, in order to display the pixel area below the threshold value without the intervention of the X-ray compensation filter, the pixel area under this X-ray imaging condition It is necessary to retract the X-ray compensation filter 4 to a pixel area equal to or larger than the threshold value, that is, to expand the opening from the current position. In this case, the only difference is whether the opening is narrowed or widened, and a description thereof will be omitted.

The X-ray image diagnostic apparatus of the first embodiment is
Since the configuration is as described above, the X-ray compensation filter 4
Can be controlled to be inserted into a position that covers a pixel region other than the pixel region suitable for the diagnosis target by following the change of the X-ray imaging condition.

Next, the second embodiment will be described with reference to FIGS.
This will be described with reference to FIG. 2 to 4 have been described in the first embodiment of the 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 image diagnostic apparatus of the present invention.

The X-ray image diagnostic apparatus of the second embodiment is
The bed 2, the X-ray generator 3, the X-ray compensation filter 4, and the I.D. I.
5, TV camera 6, image display processing unit 7, and display output unit 8
A perspective image storage unit 9, an insertion position calculation unit 10, a filter control unit 11, an attenuation amount conversion storage unit 18, and an X-ray generation control unit 14.
It has a high voltage generation unit 15, an input operation unit 16 and a central processing unit 17. The bed 2, the X-ray generator 3, the X-ray compensation filter 4, and the I.D. I. 5, TV camera 6, and image display processing unit 7
Display output unit 8, perspective image storage unit 9 and insertion position calculation unit 1
0, the filter control unit 11, the X-ray generation control unit 14, the high voltage generation unit 15, and the input operation unit 16 have been described in the first embodiment of the present invention, and therefore description thereof will be omitted. Attenuation conversion storage unit 1
Reference numeral 8 is a combination of 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, respectively.
In order to calculate the filter insertion area by using the X-ray compensation filter, 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 and copper attenuates the X-rays. It is stored after being converted from (Equation 1) and (Equation 2). The central controller 15 controls the X-ray compensation filter 4, I.V. I. 5, the television camera 6, the image display processing unit 7, the perspective 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. Then, each is controlled based on each of the above information.

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. Then, the thickness of the X-ray transmission filter is increased as the subject moves and the X-ray compensation filter 4 attenuates the X-ray attenuation amount due to the insertion of the X-ray compensation filter 4 from the attenuation amount conversion storage unit 18. The amount of attenuation by the member is read out, and the arithmetic processing unit included in the central processing unit 17 or the image display processing unit 8 calculates the fluoroscopic image data when the X-ray compensation filter 4 is not provided.
The insertion position calculation unit 10 uses the fluoroscopic image data,
The position of the X-ray compensation filter 4 is calculated based on a preset threshold value under the new X-ray imaging condition of 80 [kV], and the blade U is calculated from the difference from the current position.
The amount of movement of each part of D, L, and R is calculated for each. The filter control unit 11 moves the X-ray compensation filter 4 based on the moving amount calculated for each blade to narrow the opening. Under such arrangement condition of the X-ray compensation filter, the fluoroscopic image data is obtained under the X-ray imaging condition of the 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.

The X-ray image diagnostic apparatus of the second embodiment is
Since the configuration is as described above, the X-ray compensation filter 4
Can be controlled to be inserted into a position that covers a pixel area other than the pixel area suitable for the diagnosis target by following the change of the X-ray imaging condition, and the calculation by the attenuation amount calculation unit described in the first embodiment is unnecessary. Therefore, it is possible to more quickly follow changes in X-ray imaging conditions. Further, 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 the change of the X-ray imaging condition with a simpler structure.

Further, as the X-ray image diagnostic apparatus according to the third embodiment, the blades forming the X-compensation filter described in FIG. 2 are multiplexed in the X-ray irradiation direction to follow changes in X-ray imaging conditions. You may control it. FIG. 6 shows a configuration diagram of an X-ray compensation filter having two blades each. Each of these two blades has a pixel region where a halation phenomenon occurs, and a pixel region where a halation phenomenon does not occur but the halation phenomenon occurs immediately when the tube voltage is boosted (hereinafter referred to as “pixels where a halation phenomenon is likely to occur”). Area ")
Use to cover each of the. For example, in a pixel area where a halation phenomenon occurs, two blades are overlapped and inserted, and in a pixel area where a halation phenomenon is likely to occur, one of the two blades is inserted. As an 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, U is applied to the pixel area where the halation phenomenon is likely to occur.
Only the X-ray compensation filter composed of D, L and R is inserted, and U1 and
Insert D1, L1 and R1. Further, when the tube voltage is further boosted, U and U1, D and D1, L and L1, and R and R1 may be inserted in layers.

The X-ray image diagnostic apparatus of the third embodiment is
Since the configuration is as described above, the X-ray compensation filter 4
Can be controlled to be inserted at a position that covers a pixel area other than the pixel area suitable for the diagnosis target by following a change in the X-ray imaging condition, and a plurality of pixels can be provided according to the first and second embodiments. With the multiplexed blades, it is possible to finely follow changes in X-ray imaging conditions.

No matter how the above-mentioned respective embodiments are combined, the X-ray compensation filter 4 is placed at such a position as to follow a change in X-ray imaging conditions and cover a pixel region other than the pixel region suitable for the diagnosis target. It goes without saying that the insertion can be controlled.

[0022]

According to the present invention, the insertion position of the X-ray compensation filter is set when the X-ray compensation filter is inserted based on the X-ray imaging condition arbitrarily changed by the X-ray attenuation amount calculating means. An X-ray attenuation amount is calculated, the X-ray compensation filter insertion area calculation means calculates the pixel area based on the attenuation amount, and the X-ray compensation filter control means uses the pixel area based on the attenuation amount. Since the X-ray compensation filter is inserted or retracted, the X-ray compensation filter
Since the insertion control can be performed at a position that covers a pixel area other than the pixel area that is suitable for the diagnosis target by following a change in the radiographic conditions, the X-ray compensation filter is at an appropriate position and is suitable for diagnosis. It is possible to provide an X-ray image diagnostic apparatus capable of obtaining a fluoroscopic image.

[Brief description of drawings]

FIG. 1 is a block diagram showing a configuration example of a first embodiment of an X-ray image diagnostic apparatus of the present invention.

FIG. 2 is a structural diagram showing a configuration example of an X-ray compensation filter in FIG.

FIG. 3 is a graph showing a curve showing characteristics of tube voltage and X-ray energy absorption (relative value) under X-ray imaging conditions.

4 is an X-ray compensation filter 4 of FIG. 2 on a perspective image.
FIG. 7 is a diagram showing a display example of images before and after moving.

FIG. 5 is a block diagram showing a configuration example of a second embodiment of an X-ray image diagnostic apparatus of the invention.

FIG. 6 is a configuration diagram of an X-ray compensation filter having two blades each.

[Explanation of symbols]

 11 Filter Control Section 12 Attenuation Rate Storage Section 13 Attenuation Calculation Section 18 Attenuation Conversion Storage Section

Claims (4)

[Claims] 1. An X-ray generation unit for generating X-rays, X-ray control means for controlling X-ray imaging conditions by the X-rays, and an X-ray attenuation unit arranged on the side irradiated with the X-rays. An X-ray compensation filter formed of a member, and the X-ray which is arranged so as to face the X-ray generation unit with the subject in between and which has passed through the subject.
An image intensifier for receiving a line and converting it into an optical image, a television camera optically joined to the image intensifier for photographing the optical image and outputting a perspective image, and the television camera connected to the television camera A fluoroscopic image storage means for storing a fluoroscopic image, and a threshold value storage means for storing a pixel value causing a halation phenomenon of the X-ray fluoroscopic image corresponding to the X-ray imaging condition as a threshold value.
An insertion area calculation means that is connected to the perspective image storage means and the threshold value storage means and that reads out the perspective image and calculates a pixel area equal to or more than the threshold value as an insertion area of the X-ray compensation filter; In an X-ray image diagnostic apparatus including a filter control unit that is respectively connected to a line compensation filter and the insertion region calculation unit and that inserts the X-ray compensation filter into the insertion region, the X-ray compensation filter is a first X-ray imaging condition. When the X-ray control means is set to a second X-ray photography condition different from the first X-ray photography condition, the second X-ray control means is connected to the X-ray control means. The X by the X-ray compensation filter arranged corresponding to the first X-ray imaging condition of the imaging condition.
Attenuation amount calculation means for calculating the attenuation amount of a ray, and a conversion image which is connected to the attenuation amount calculation means and is converted into each pixel value of the X-ray fluoroscopic image when the X-ray compensation filter is not inserted based on the attenuation amount. The insertion area calculating means is also connected to the image converting means, and the pixel area from the threshold value corresponding to the X-ray imaging condition of the converted image to the threshold value or more is the X-ray compensation filter. The second X of
An X-ray image diagnostic apparatus, wherein the filter control means inserts the X-ray compensation filter into an insertion area corresponding to the second X-ray imaging condition, which is calculated as an insertion area corresponding to the X-ray imaging condition. 2. An X-ray generation unit for generating X-rays, X-ray control means for controlling X-ray imaging conditions by the X-rays, and an X-ray attenuation unit arranged on the side irradiated with the X-rays. An X-ray compensation filter formed of a member, and the X-ray which is arranged so as to face the X-ray generation unit with the subject in between and which has passed through the subject.
An image intensifier for receiving a line and converting it into an optical image, a television camera optically joined to the image intensifier for photographing the optical image and outputting a perspective image, and the television camera connected to the television camera A fluoroscopic image storage means for storing a fluoroscopic image, and a threshold value storage means for storing a pixel value causing a halation phenomenon of the X-ray fluoroscopic image corresponding to the X-ray imaging condition as a threshold value.
An insertion area calculation means that is connected to the perspective image storage means and the threshold value storage means and that reads out the perspective image and calculates a pixel area equal to or more than the threshold value as an insertion area of the X-ray compensation filter; In an X-ray image diagnostic apparatus including a filter control unit that is respectively connected to a line compensation filter and the insertion region calculation unit and that inserts the X-ray compensation filter into the insertion region, the X-ray compensation filter is a first X-ray imaging condition. When the X-ray control means is set to a second X-ray photography condition different from the first X-ray photography condition, the second X-ray control means is connected to the X-ray control means. The X by the X-ray compensation filter arranged corresponding to the first X-ray imaging condition of the imaging condition.
Attenuation amount storage means for pre-calculating and storing the attenuation amount of the line,
The insertion area calculation means is connected to the attenuation amount storage means, and includes image conversion means for converting each pixel value of the X-ray fluoroscopic image when the X-ray compensation filter is not inserted based on the attenuation amount into a converted image. Is also connected to the image conversion means, and a pixel region from the threshold value corresponding to the X-ray imaging condition of the converted image to the threshold value or more is inserted into the X-ray compensation filter corresponding to the second X-ray imaging condition. An X-ray image diagnostic apparatus, characterized in that the filter control means inserts the X-ray compensation filter into an insertion region corresponding to the second X-ray imaging condition. 3. The X-ray imaging condition according to claim 1, wherein the X-ray imaging condition is set based on a thickness at which the X-ray is transmitted to the subject. Line image diagnostic equipment. 4. The X-ray compensation filter is formed by stacking a plurality of the attenuation members in the X-ray irradiation direction, and the plurality of attenuation members are individually / integrally controlled, and the image The X-ray diagnostic imaging apparatus according to any one of claims 1 to 3, wherein the X-rays received by the tensifier can be arbitrarily attenuated.