JP2002172112A - X-ray ct scanner for fast photographing - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an X-ray CT scanner capable of photographing a tomographic image in a short scanning time without accelerating the rotation of a frame. SOLUTION: In the X-ray CT scanner, three X-ray equipments 1A, 1B and 1C for irradiating a patient on a bed with X-rays are arranged in a plane which is on the circumference centered on a rotary axis and is orthogonal to the rotary axis. In addition, the three equipments 1A, 1B and 1C are positioned respectively on reference lines passing through the rotary axis and forming 120 deg. with each other, three detector strings 6A, 6B and 6C are arranged on the circumference similarly opposing these equipments 1A, 1B and 1C, and both of them are rotated simultaneously by a rotation mechanism. X-rays emitted from the equipments 1A, 1B and 1C and transmitted through the patient are detected by the detector strings 6A, 6B and 6C to re-construct a single tomographic image by detection signals from the detector strings.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

The present invention relates to an X-ray CT scanner, and more particularly, to an X-ray CT scanner having a plurality of X-ray sources.

[0002]

2. Description of the Related Art An X-ray CT scanner irradiates a subject with X-rays, detects X-rays transmitted through the subject, processes the signal, and thereby forms a tomographic image of a region of interest (ROI). It is known as a rebuilding device.

An example of such an X-ray CT scanner is shown in FIG. The conventional X-ray CT scanner shown in FIG. 6 includes a single X-ray tube device 1 as an X-ray source for generating X-rays. In this X-ray CT scanner, X-rays generated from the X-ray tube device 1 are applied to a subject 4 placed on a top 5 via a slit 2 for limiting an intensity distribution. The X-rays that have passed through the slit 2 travel along an X-ray path indicated by reference numeral 3, and as a result, a substantially fan-shaped X-ray is to be displayed as a tomographic image as shown in FIG. ROI). The X-rays that have passed through the region of interest are incident on a detector array 6 in which a number of detectors are arranged along an arc, and are converted into detection signals by the detector array 6. This detection signal is supplied to the data collection device 7, amplified, and A / D converted. The digital detection signal from the data collection device 7 is provided as data to a computer (not shown). Computer
The X-ray absorptivity of each part of the region of interest of the subject is calculated from the detection signal as the received data, and a tomographic image of the region of interest of the subject is obtained as image data from the calculated value. A tomographic image of the area is displayed.

In order to obtain a tomographic image of the subject 4, the X-ray tube device 1, the slit 2 and the detector array 6 need to be rotated around the subject 4. 1, the slit 2, the detector array 6, and the data collection device 7 are integrally fixed to a rotating frame 8, and the rotating frame 8 is rotatably supported by a fixed frame 9.

[0005] X-ray tube device 1, slit 2 and detector array 6
Is rotated around the rotation center O without changing its relative position, so that X-rays are radiated from around the region of interest of the subject. From the X-ray absorptivity of each part, an image of each part is obtained as a tomographic image. Will be done. That is, such X-ray CT
In the scanner, the X-ray tube apparatus 1 and the detector row 6 are opposed to each other and rotated around the subject 4, and projection data covering all angles of all points in the examination section of the subject 4 is obtained. From these data, a tomographic image is obtained from these data by a data reconstruction program programmed in advance. here,
The example in which the detector array 6 is rotated to face the X-ray tube apparatus 1 has been described. However, if the detector array 6 is arranged on the entire circumference, the detector array is fixed. Is also good.

[0006]

The X-ray C as described above
The T scanner has a problem in that, if the subject moves during scanning, motion artifacts occur in the tomographic image. Therefore, it is required that the subject not only move but also hold his breath during the scan.

[0007] In order to reduce the pain of the subject being forced to hold his / her breath, or to reduce motion artifacts caused by involuntary movements of organs that cannot be stopped by the breath, the examination speed has been conventionally improved. Great efforts have been made to make this happen.

[0008] One of the improvements to improve the inspection speed
One is to increase the rotation speed of the gantry. However, in such an X-ray CT scanner, heavy parts such as the X-ray tube device 1, the slit 2, the detector array 6, the data acquisition device 7, and the rotating gantry 8 must be rotated, and the rotation speed It is said that there is a mechanical limit in increasing the amount of methane. Here, assuming that the time of one rotation of these rotating parts is T seconds, the centrifugal acceleration during rotation is approximately (3
/ T ² ) G, and there is a problem that a large centrifugal force is applied to the X-ray tube device 1 or other rotating parts.

When the rotational speed of the gantry is increased, the gantry must be mounted in order to prevent an increase in image noise of the tomographic image.
The X-ray dose emitted from the X-ray tube apparatus 1 to the subject during rotation needs to be substantially the same as when the rotation speed of the gantry is not increased. Therefore, the X-ray tube device 1 is required to have a larger X-ray short-time output power performance as the time T of one rotation becomes shorter. Therefore, the X-ray tube device 1
There is a need to increase the diameter of the X-ray generation target to increase the heat-resistant load performance. As a result, the X-ray tube device 1 becomes heavy and the centrifugal force increases due to the rotation of the gantry. There is.

At present, in the highest class machine, the time T per rotation T =
A 0.5 second performance has been achieved. The centrifugal acceleration in this case is about 12 G, but it is considered that the performance is almost the limit. Therefore, the shortest scan time per one tomographic image is 0.5 seconds in the full scan mode and about 0.3 seconds in the half scan mode.

Another improvement for increasing the inspection speed is to continuously rotate the rotating gantry 8 and to continuously move the table 5 on which the subject 4 is placed in the direction of the rotation axis. A helical scan for obtaining a plurality of tomographic images along the body axis direction of the subject 4 by collecting the tomographic image data of the subject 4 in a spiral (helical) manner. In connection with the invention of the helical scan, an improvement in which the number of detector rows is increased as disclosed in JP-A-63-62215, and
With a plurality of X-ray tube devices as disclosed in
Improvements have been proposed for taking multiple helical scan images in parallel.

However, the scanning time spent per one tomographic image is still limited by the rotational speed of the gantry. In the currently realized X-ray CT scanner, the gantry rotation cycle T is the shortest in 0.5 seconds, so that the scan time per tomographic image by helical scan is the case where 360 ° interpolation is adopted. The shortest time is 0.25 seconds when the 0.5 second, 180 ° interpolation method is adopted. In the case of helical scan, the subject 4
In order to increase the number of a plurality of tomographic images along the body axis direction of the subject 4, in other words, to increase the resolution in the direction along the body axis direction of the subject 4 and to increase the examination accuracy, the gantry rotation speed must be increased. Although it is necessary to make it larger, there is a problem that there is a limit as described above.

As described above, in order to increase the inspection speed by the conventional X-ray CT scanner and increase the inspection accuracy, it is necessary to increase the rotation speed of the gantry. Has occurred.

SUMMARY OF THE INVENTION The present invention has been made in view of the above circumstances, and has as its object to capture individual tomographic images in a shorter scan time than in the past without increasing the gantry rotation speed. An object of the present invention is to provide an X-ray CT scanner for high-speed imaging capable of performing high-speed imaging.

[0015]

According to the present invention, there are provided a plurality of X-ray beam generating sources for irradiating X-rays to a subject on a bed with at least two X-ray sources, and a plurality of X-ray beam sources. An X-ray CT scanner comprising: a detector array for detecting X-rays emitted from a source; and a rotating unit for rotating the X-ray beam source around the subject. The beam generation source is arranged in a plane perpendicular to the rotation axis, and is simultaneously irradiated from the plurality of X-ray beam generation sources, and detects X-rays transmitted through the subject by the detector array to detect the X-rays. An X-ray CT scanner is provided which reconstructs and outputs data of one tomographic image by using a detection signal from a device row as data.

[0016]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS An X-ray CT scanner according to an embodiment of the present invention will be described below with reference to the drawings.

FIG. 1 and FIG. 2 show an X-ray CT scanner according to an embodiment of the present invention. FIGS. 3 to 5 show an X-ray CT scanner according to another embodiment of the present invention.

An X-ray CT scanner according to an embodiment of the present invention includes N X-ray tube apparatuses 1A to 1N as X-ray sources for generating X-rays. Each of the X-ray tube apparatuses 1A to 1N includes a rotary anode X-ray tube that rotatably supports an anode target by a slide bearing using a liquid metal as a lubricant. As explained later, this N is
5 or less, and preferably 2 or 3. The X-ray CT scanner shown in FIGS. 1 and 2 shows an embodiment including three (N = 3) X-ray tube apparatuses 1A, 1B, and 1C. Three (N = 3) slits 2A, 2B, and 2C corresponding to the X-ray tube apparatuses 1A, 1B, and 1C are provided on the X-ray emission sides of the three X-ray tube apparatuses 1A, 1B, and 1C, respectively. Are provided, and these X
Detector arrays 6A, 6 facing the tube devices 1A, 1B, 1C
B and 6C are provided, and the detector rows 6A, 6B and 6 are provided.
C is provided with data collection devices 7A, 7B, 7C for the detector rows 6A, 6B and 6C. These X-ray tube apparatuses 1A, 1B, 1C, slits 2A, 2B, 2C,
Detector rows 6A, 6B and 6C, data collection devices 7A and 7
B and 7C are integrally fixed to a rotating gantry 8, which has a center of rotation O, is rotatably supported by a fixed gantry 9, and is rotated by a rotating mechanism (not shown). Therefore, the X-ray tube apparatuses 1A, 1B, 1C and the detector rows 6A,
6B and 6C will be rotated substantially synchronously. The object 4 is moved so that the rotation center O passes through the object 4.
Is provided.

In the X-ray CT scanner shown in FIGS. 1 and 2, an X-ray tube apparatus 1A, 1
The X-ray tube apparatuses 1A, 1B and 1C are fixed to the rotating gantry 8 so that fan-shaped (fan-shaped) X-rays generated from B and 1C and passing through the slits 2A, 2B and 2C pass.
The subject 4 cut along a plane orthogonal to the rotation center O is a region of interest, and a cut surface of the region of interest is reconstructed as a tomographic image from the detected X-rays.

The X-ray tube apparatuses 1A, 1B, and 1C are
Are arranged in a plane orthogonal to the rotation center O so as to be rotationally symmetrical about the center of rotation, and when N is an odd number, the center lines C0 of the fan-shaped X-rays make an angle β equal to each other. The X-ray tube apparatuses 1A, 1B, and 1C are arranged in the. It is preferable to provide an adjustment mechanism (not shown) for adjusting the X-ray tube apparatuses 1A, 1B, and 1C so as to be arranged at an angle β around the rotation center. In the X-ray CT scanner shown in FIG. 1, since N is 3, the angle β is 120 °.

FIG. 3 shows two X-ray tube apparatuses 1A, 1B and two slits 2 where N is an even number 2.
A, 2B and X provided with two detector rows 6A, 6B
A line CT scanner is shown. When N is an even number, the X-ray tube apparatuses 1A, 1B,
When it is assumed that the slits 2A and 2B and the detector rows 6A and 6B are arranged, the X-ray tube apparatuses 1A and 1B are arranged such that the center lines C0 of the fan-shaped X-rays form an equal angle β.
Can not be placed. That is, the X-ray tube apparatuses 1A and 1B, the slits 2A and 2B are arranged in a plane orthogonal to the rotation center O.
When the detector rows 6A and 6B are arranged, each combination of the X-ray tube apparatuses 1A and 1B and the slits 2A and 2B is connected to one of the corresponding detector rows 6A and 6B via the rotation center. It is required that the X-ray tube apparatuses 1A and 1B be arranged facing each other because of this requirement. If the angles β are equal to each other in the case where N is an even number, the X-ray tube apparatuses 1A and 1B always face each other. In the arrangement shown in FIG. 3, the center line C0 passing through the X-ray tube apparatuses 1A and 1B has a different angle β, and forms an angle of 120 ° or 240 ° as an example.

As shown in FIG. 4, when the X-ray tube apparatuses 1A and 1B, the slits 2A and 2B and the detector array 6 do not need to be arranged in a plane orthogonal to the rotation center O, the X-ray tube apparatus The X-ray tube apparatuses 1A, 1B and 1C may be arranged such that the center lines C0 of the fan-shaped X-rays passing through 1A and 1B form an equal angle β. In the X-ray CT scanner shown in FIG. 4, the detector row 6 is arranged in a ring-shaped first plane orthogonal to the rotation center O, and the X-ray tube apparatuses 1A and 1B and the slits 2A and 2B rotate. It is arranged in a second plane parallel to the first plane orthogonal to the center O. With this scanner,
The X-ray tube devices 1A and 1B generate the slits 2A and 2A
The fan-shaped X-ray that has passed through B is incident on the subject 4 at a slight angle with respect to a plane orthogonal to the rotation center O, and is incident on the ring-shaped detector array 6.

In the X-ray CT scanner of the present invention, since the amount of scattered X-rays incident on the detector array 6 is larger than that of the conventional apparatus, the X-ray CT scanner shown in FIGS. As shown in FIG. 7, a detector 16 for correcting a detection value is provided adjacent to the detector array 6A, detects X-rays 10 scattered in the subject 4, and outputs the detector array based on the output from the detector 16. Preferably, the output from 6A is corrected to remove the effects of scattered X-rays. That is, not only the detection signal from the detector array 6A but also the detection signal from the detector 16 is supplied to the data collection device 7A, and the detection signal from the detector array 6A is corrected based on the detection signal from the detector 16. It is preferable to improve the detection accuracy.

In order to reduce the probability of occurrence of a failure in the X-ray tube device, the reliability of the rotating mechanism is high as described above.
It is advantageous to employ an X-ray tube device using a liquid metal lubricated plain bearing.

In such an X-ray CT scanner, the X-rays generated from each of the X-ray tube apparatuses 1A, 1B and 1C correspond to limit the intensity distribution as shown in FIGS. The subject 4 placed on the top 5 is irradiated through the slits 2A, 2B, and 2C. Slit 2A,
The X-rays that have passed through 2B and 2C travel along an X-ray path indicated by reference numeral 3, and as a result, as shown in FIG. It will pass through the region (ROI). The X-rays that have passed through the region of interest are incident on detector rows 6A, 6B, 6C in which a number of detectors are arranged along an arc, and are converted into detection signals by the detector rows 6A, 6B, 6C. . This detection signal is supplied to the data collection devices 7A, 7B, 7C, amplified, and A / D converted. This data collection device 7
Digital detection signals from A, 7B and 7C are provided as data to a computer (not shown). The computer calculates the X-ray absorptance of each part of the region of interest of the subject from the detection signal as the received data, obtains a tomographic image of the region of interest of the subject as image data from the calculated value,
A tomographic image of the region of interest is displayed on a display device (not shown).

X-ray tube apparatus 1A, 1B, 1C, slit 2
A, 2B, and 2C and the detector rows 6A, 6B, and 6C are rotated around the rotation center O without changing their relative positions, so that X-rays are radiated from around the region of interest of the subject. From the X-ray absorptance, an image of each part is obtained as a tomographic image. That is, in such an X-ray CT scanner, the X-ray tube apparatuses 1A, 1B, 1C and the detector rows 6A, 6
B and 6C are opposed to each other and rotated around the subject 4 to obtain projection data covering all angles of all points in the examination section of the subject 4 and pre-programmed from these data. A tomographic image is obtained by the data reconstruction program. Here, the detector rows 6A, 6B, 6C are X
The example in which the detector array 6 is rotated so as to face the wire tube device 1 has been described. However, as long as the detector array 6 is arranged on the entire circumference, the detector array may be fixed.

In the X-ray CT scanner shown in FIGS. 1 and 2, three X-ray tubes 1A, 1B and 1C, and three slits 2A corresponding to the three X-ray tubes 1A, 1B and 1C, 2
B and 2C, and these X-ray tube apparatuses 1A,
1B, 1C, three detector rows 6A, 6B and 6
C, the gantry 8 is moved three times per rotation.
At a speed of / 4 second, the rotation of the subject 4 is slightly (360 °
/ 3) By rotating, in the conventional device, 0.25
It is possible to collect tomographic image data equivalent to one tomographic image obtained by 360 ° interpolation obtained by one rotation per second. Actually, as described above, it is considered that such a high-speed rotation of the gantry 8 is practically impossible with the conventional X-ray CT scanner.

Further, the rotation of the pedestal is slightly ((360 ° / 6) + α) at a speed of 3/4 second per rotation.
°) By rotation, 180 obtained by rotating (0.5 + α) at a speed of 0.25 seconds / rotation with the conventional device.
° A tomographic image equivalent to one tomographic image by the interpolation method can be obtained. In this case, one tomographic image can be obtained in about 0.125 seconds. Similarly, it is considered that such a rotation of the gantry 8 is impossible in a conventional X-ray CT scanner.

Even if the amount of X-rays radiated by one X-ray tube is reduced to 1/3 of the conventional value, it is possible to obtain an image having the same clarity as the conventional case.

In the X-ray CT scanner shown in FIGS. 1 and 2, three X-ray tube apparatuses 1A, 1B, and 1C correspond to three X-ray tube apparatuses.
FIG. 3 shows a case where three slits 2A, 2B and 2C are provided, and three detector rows 6A, 6B and 6C are provided in opposition to these X-ray tube apparatuses 1A, 1B and 1C. In the X-ray CT scanner, two slits 2A, 2B corresponding to the two X-ray tube apparatuses 1A, 1B
Is provided, and two detector rows 6A and 6B are provided to face these X-ray tube apparatuses 1A and 1B. However, N X-ray tube apparatuses and N Next, the case where N slits and N detector rows are provided will be described, and the optimum value of N will be described. In the following description, a calculation example in the case where the angle Ω at which the detector is viewed from the rotation center O is 90 ° (Ω = 90 °) as shown in FIG. 1 will be described.

Calculation of Effect Estimation (Determining the Optimum Value of N) For simplicity, it is assumed that the detector rows are arranged on the entire circumference as shown in FIG. In this case, even when the number of X-ray tubes is even, the X-ray tubes can be arranged at symmetric positions.

The effects were estimated as follows.

N: Number of X-ray tubes.

Ω: width of each detector. Expressed as an angle (°) at which the detector is viewed from the rotation center. The larger this angle is, the shorter the required X-ray dose can be applied. In the case of a conventional device (N = 1), this angle differs from device to device, but is approximately 90 °.

Ω = 90 when N ≦ 3 Ω = (360 / N) −30 when N ≧ 3 I: The radiation X-ray dose I is represented by a tube current value (mA) (conventional 50).
0 and 500 · k / N in the case of the present invention).

X: an amount proportional to the X-ray dose incident on all detectors per second assuming that the gantry is stationary x = I · Ω · N = (500 k / N) ((360 / N) −30) N = (180000k / N) -15000k However, when N ≦ 5, x = I · Ω · N = 30000k Conventional value is x ₀ = 500 × 90 = 45000 θ ′: gantry rotation speed (360/0 in the conventional case) .5) Δθ: the gantry rotation angle 36 that is the minimum required for image data collection
0 / N (image equivalent to the conventional 360 ° interpolation method).

X: a quantity proportional to the X-ray dose incident on all detectors, which is the minimum required for image data (conventionally, one rotation) X = x · Δθ / θ ′ = (64800000 k / N
^{2 θ ') - (5400000k /} Nθ') However, in the case of N ≦ 3 X = x · Δθ / θ '= 540000
0k / θ ′ The conventional value is X ₀ = 45000 × 360 / (360/0.
5) = 22,500 (1) By setting X = X ₀ , first, f for each N
(N) = θ ′ / k is obtained. The results are as follows.

[0038]

[Table 1]

That is, k must be increased as θ ′ increases, in accordance with f (N) = θ ′ / k.

Here, θ ′ = 360 / T, and I
= 500 · k / N, I = 180000 / TNf (N)-(2) Estimation of tube current and gantry rotation speed 1 Time required for tomographic image data collection t = Δθ / θ '= 3
Since it is desired that 60 / Nθ ′ ≦ 0.5, 720 / N ≦ θ ′.

When this equation is further modified, T ≦ N / 2 ----- (3) Summary of estimation results for each N The following results are obtained from the above equations.

[0042]

[Table 2]

In all cases where N is 2 or more, the gantry rotation speed can be reduced as compared with the conventional case. The gantry rotation speed required to capture one image data in 0.25 seconds is as follows.
It can be seen that the gantry rotation technology realized by the current device can sufficiently cope with the problem.

On the other hand, to minimize the tube current I, N =
It turns out that it is necessary to choose 3.

In the case of N = 2, an image equivalent to a conventional 0.5-second scan can be taken with a smaller tube current, but an image equivalent to a 0.25-second scan, which cannot be realized by the conventional apparatus, is a tube-like image. Since it is necessary to make the current higher than in the past, it is still difficult to realize the current technology level. N =
By setting it to 3, 0.2 which cannot be realized by the conventional device
An image equivalent to a 5-second scan can be taken with a lower tube current than before. Even if N is increased to 3 or more, it is possible to capture an image equivalent to 0.25 second scan, but the required tube current is increased compared to the case of N = 3, and there is no merit. I understand.

In the X-ray CT scanner shown in FIGS. 1 and 2, three X-ray tubes are used. Even if one of them fails, the remaining two tubes are used until a substitute tube is brought in. With the use of individual pieces, it is possible to continue the inspection without interrupting it while maintaining the reasonable merits. Even if two of the X-ray tubes fail, the remaining one can still perform the conventional inspection, and various operations can be set in the X-ray CT scanner in advance based on the number of usable X-ray tubes. Can be dealt with. By making the X-ray CT scanner operable in various operation modes based on the number of usable X-ray tubes, the probability that three X-ray tubes fail simultaneously is extremely low. Accordingly, the operation rate of the X-ray CT scanner can be stably increased. Further, in the above-described embodiment, a mechanism for adjusting the positions of the respective X-ray tubes and the corresponding detectors in the direction of the rotational radius is provided so that the positions in the direction of the rotational radius can be variably set. Is preferred. It is possible to make a trade-off between increasing the inspection area and increasing the resolution. If the outputs of the plurality of X-ray tubes are made the same, it is not necessary to perform data correction before combining the output data of the detectors. For that, each X
The tube voltage and the tube current of the tube must be the same. In order to make the tube voltage of each X-ray tube the same, it is desirable to apply a voltage to each X-ray tube in parallel using the same high-voltage power supply. In order to make the tube current of each X-ray tube the same, it is desirable to use the same filament heating power source, connect each X-ray tube in series, and supply current.

Further, in the above-described embodiment, a single scan has been described. However, a similar effect can be naturally obtained by applying the present invention to a helical scan. That is,
X-ray tube apparatuses 1A, 1B, 1C and detector rows 6A, 6B,
During the rotation of 6C, the subject is helically scanned by the X-ray beam by the top plate 5 being moved at a constant speed along the rotation center axis O by a moving mechanism (not shown), and successive tomographic images are sequentially formed. Data will be obtained.

[0048]

According to the present invention, there is provided an X-ray CT scanner capable of capturing an image in a shorter time than before, and obtaining an image with high instantaneousness and little motion blur. This X-ray CT scanner greatly contributes to the improvement of diagnostic performance particularly in cardiac examination. Also, since the rotation speed of the gantry can be made lower than before, the mechanical load on the gantry is reduced,
The device can be made compact.

Further, according to the X-ray CT scanner of the present invention, the mechanical load (centrifugal force) and the heat load (tube current) on the X-ray tube are reduced. Therefore, when adopting an X-ray tube using a sliding bearing using liquid metal as a lubricant as a bearing,
Since it is permissible to make the diameter of the bearing smaller, it is possible to rotate at a higher speed. Furthermore, according to the X-ray CT scanner of the present invention, the anode rotation speed of the X-ray tube can be increased, and the tube current can be reduced. It is also possible to obtain.

Even when the imaging time per tomographic image is suppressed to the same level as the conventional one, the X-ray dose radiated by one X-ray tube can be reduced to 1/3 of the conventional value. Is made smaller, and a higher-resolution tomographic image can be obtained.

Further, since the heat load on the X-ray tube is reduced,
The waiting time for cooling the anode target can be reduced. As a result, the waiting time between tests is reduced, and the throughput (number of patient processes) is improved.

[Brief description of the drawings]

FIG. 1 is an X-ray CT for high-speed imaging according to a first embodiment of the present invention.
It is a front view which shows a scanner schematically.

FIG. 2 is a cross-sectional view schematically showing a cross section of the X-ray CT scanner for high-speed imaging shown in FIG.

FIG. 3 is an X-ray CT for high-speed imaging according to Embodiment 2 of the present invention;
It is a front view which shows a scanner schematically.

FIG. 4 is an X-ray CT for high-speed imaging according to a third embodiment of the present invention.
It is sectional drawing which shows the cross section of a scanner roughly.

FIG. 5 is an X-ray C for high-speed imaging according to a modified embodiment of the present invention.
It is sectional drawing which shows the cross section of a T scanner roughly.

FIG. 6 is a front view schematically showing a conventional high-speed X-ray CT scanner.

[Explanation of symbols]

 1A, 1B, 1C. . . X-ray tube apparatus 2A, 2B, 2C. . . Slit 3. . . 3. Irradiation X-ray path . . Subject 5. . . Top plate 6A, 6B, 6C. . . Detector row 16. . . 6. Scattered ray detector row . . Data collection device 8. . . Rotation stand 9. . . Fixed stand 10. . . Scattered X-ray path

[Procedure amendment]

[Submission date] February 19, 2001 (2001.2.1)
9)

[Procedure amendment 1]

[Document name to be amended] Statement

[Correction target item name] Claims

[Correction method] Change

[Correction contents]

[Claims]

Claims (9)

[Claims] 1. A plurality of X-ray beam generating sources for irradiating an object on a couch with X-rays and detecting X-rays emitted from the plurality of X-ray beam generating sources. An X-ray CT scanner, comprising: a detector array; and a rotating unit that rotates the X-ray beam source around the subject. The plurality of X-ray beam sources are perpendicular to a rotation axis. X-rays that are arranged in a plane and are simultaneously irradiated from the plurality of X-ray beam sources and transmitted through the subject are detected by the detector array, and a detection signal from the detector array is used as data as 1 data. An X-ray CT scanner reconstructing and outputting tomographic image data. 2. An X-ray CT scanner according to claim 1, wherein each of said plurality of X-ray beam sources is an X-ray tube device. 3. The X-ray tube apparatus according to claim 2, wherein each of said plurality of X-ray beam generating sources is a rotary anode type X-ray tube apparatus which rotates an anode target by a slide bearing using liquid metal as a lubricant. X-ray CT scanner. 4. A plurality of detector rows are arranged corresponding to a plurality of X-ray beam sources, respectively, and are rotated by the rotating means in synchronization with the corresponding X-ray beam sources. The X-ray CT scanner according to claim 2 or 3, wherein: 5. The X-ray CT scanner according to claim 1, wherein said detector array is configured by arranging detectors having an inner surface as a detection surface in an arc shape. 6. A helical scan of an object with an X-ray beam by rotating the plurality of X-ray beam sources and moving a bed on which the object is mounted along a rotation axis. 6. The X-ray CT scanner according to claim 1, wherein: 7. The apparatus according to claim 6, further comprising setting means for setting an interval of the X-ray beam generation source around a rotation axis.
X-ray CT scanner. 8. An X-ray CT scanner according to claim 1, wherein said detector row is a two-dimensional detector in which detection segments are two-dimensionally arranged. 9. The detector row is a ring-shaped detector row in which detection segments are circumferentially arranged on a first plane orthogonal to the rotation axis around the rotation axis, and wherein the X-ray beam generation is performed. The source is located in a second plane substantially parallel to the first plane, and X-rays from the X-ray beam source are incident on the detector array at a slight angle to the first plane. 2. The X-ray CT scanner according to claim 1, wherein the scanning is performed.