JPH09313470A - X-ray diagnostic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To make a stereo-compatible X-ray diagnostic device portable by controlling voltage applied to the primary side of a stepup transformer for controlling the pulse width of an X-ray as well as timing for exposure thereto. SOLUTION: An inverter frequency signal 63, a pulse control signal 65 and an exposure control signal 67 are supplied from an X-ray controller 53 to an inverter control circuit 55, and an inverter control signal 69 as a logical sum thereof is fed from the inverter control circuit 55 to an inverter 45. Also, the commercial alternating current of a commercial AC power supply 42 is rectified into direct current via a rectifier circuit 43, and converted to high-frequency alternating current via the inverter 45 for application to the primary side of the stepup transformer 49 of a stepup.rectifier circuit 47. In addition, high voltage after raised with the stepup transformer 49 and a Cockcroft-Walton circuit 51 as well as full-wave rectified with the circuit 51 is applied across the anode and filament of an X-ray tube.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an X-ray diagnostic apparatus capable of stereo see-through.

[0002]

2. Description of the Related Art In the field of X-ray diagnosis, there is a stereoscopic fluoroscopic technique. This is an X with two focal points, one for the right eye and one for the left eye
It is said that an observer can recognize the three-dimensional structure of an object by irradiating the subject with X-rays alternately from two focal points using a ray tube and observing the two images obtained with the right eye and the left eye, respectively. It is a thing. The system having the stereo see-through function tends to be large and heavy as a device.
As shown in FIG. 1, it is exclusively applied to a stationary type X-ray apparatus for a circulator.

An X-ray high voltage device for driving a stereo-compatible two-focus X-ray tube has a high voltage (about ± 75 KV).
In addition to the high-voltage generator for generating X-rays, a controller for controlling the pulse width of X-rays and the timing of exposure and for switching the left and right X-ray focal points are provided. Traditionally,
These controls are performed on the secondary side of the step-up transformer in the high voltage generator. Therefore, it is necessary to make all the elements compatible with the high voltage and a large amount of insulating oil, and as a whole, It will be extremely large and heavy.
Therefore, it is housed in its own wall cabinet.

There are three high-voltage cables with a diameter of about 20 mm between the X-ray tube and the X-ray high-voltage device.
In the case of a floor-standing device, it is led under the floor, and in the case of a ceiling suspension device, it is led to the back of the ceiling, and even the X-ray high-voltage device in the cabinet is handled. The connection to the X-ray tube and the connection to the X-ray high voltage device use a high pressure bushing, which is also quite large in shape to prevent discharge. As a result, the stereo X-ray tube also becomes large. From the above, the X-ray diagnostic apparatus having the stereo function has been limited to the stationary apparatus.

Further, in the conventional stereo compatible X-ray diagnostic apparatus, the X-ray conditions such as the tube voltage, the tube current and the X-ray pulse width are
It was controlled to have the same value for the left and right focal points. The reason for this is that the development of stereo photography / fluoroscopy was originally made for specific parts such as the head and abdomen, that is, in these parts, X-ray attenuation characteristics are almost equal on the left and right sides, Unless the right and left X-ray conditions are set to the same, the image quality such as brightness and contrast will be shifted left and right, which makes stereoscopic viewing difficult. But,
From the opposite viewpoint, this has a problem that the application range of stereoscopic fluoroscopy is limited only to objects whose X-ray attenuation characteristics are almost the same on the left and right.

[0006]

SUMMARY OF THE INVENTION It is an object of the present invention to provide a stereo compatible X-ray diagnostic apparatus with portability.

[0007]

According to the present invention, a high voltage boosted by a boosting transformer is applied to an X-ray tube to irradiate X-rays, and an image is generated based on the X-rays transmitted through a subject. In the X-ray diagnostic apparatus, the voltage applied to the primary side of the step-up transformer is controlled to control the pulse width of X-ray and the timing of irradiation.

The present invention is an X-ray diagnostic apparatus for intermittently irradiating X-rays from an X-ray tube and repeatedly generating an image based on the X-rays transmitted through an object. A constant filament current is continuously supplied to the filament of the X-ray tube during the period.

According to the present invention, a stereo compatible bifocal X-ray tube is attached to one end of the C-arm, and a means for imaging the X-ray transmitted through the subject is attached to the other end of the C-arm, and the line connecting the bifocals is formed. The X-ray tube is fixed to the C arm so as to be parallel to the C arm.

The present invention is an X-ray diagnostic apparatus having stereo-compatible right-eye X-ray generation means and left-eye X-ray generation means, and at least one of tube voltage, tube current, and X-ray pulse width.
One of them can be individually adjusted with respect to the X-ray generating means for the right eye and the X-ray generating means for the left eye. (Operation) The pulse width of the X-ray and the timing control of the irradiation are performed on the primary side of the step-up transformer. Therefore, this control element does not need to be compatible with high voltage, and a large amount of insulating oil is not required, so that it is possible to realize downsizing and weight saving, which can contribute to portability of the X-ray diagnostic apparatus.

The filament current is continuously supplied to the filament of the X-ray tube even during the rest period of the X-ray irradiation, and the filament is maintained in the heated state. Therefore,
There is no need to wait for the filament to heat up,
X-rays are emitted in synchronism with ON / OFF of the tube voltage.

By fixing the X-ray tube to the C-arm,
The rotation mechanism and slide mechanism of the X-ray tube are unnecessary, and the size and weight can be reduced accordingly. Further, if the X-ray tube is fixed to the C-arm, the standing position and the orientation of the operator are restricted with respect to the orientation of the C-arm (bifocal orientation) from the viewpoint of stereoscopic vision. In addition, such a layout can reduce the installation space of the device and the working space of the operator.
Therefore, it is suitable for a portable X-ray diagnostic apparatus.

At least one of the tube voltage, the tube current, and the X-ray pulse width can be adjusted separately by the X-ray generating means for the right eye and the X-ray generating means for the left eye. Even when the left and right X-ray attenuation amounts are extremely different, the left and right images can be adjusted to have the same image quality, and easy stereoscopic viewing is possible. This is important for a portable X-ray diagnostic apparatus which is often used in an emergency.

Since such an X-ray diagnostic apparatus can be made compact and lightweight, it can be mounted on a vehicle and can be freely moved to a required place. Therefore, in case of an emergency, the stereo is not changed and the stereo is performed on the spot. Fluoroscopic diagnosis and surgery can be performed.

[0015]

BEST MODE FOR CARRYING OUT THE INVENTION An embodiment of a portable X-ray diagnostic apparatus for stereoscopic fluoroscopy according to the present invention will be described below with reference to the drawings. FIG. 1 shows a schematic configuration of the X-ray diagnostic apparatus according to this embodiment. The X-ray tube 13 has two filaments so that stereoscopic observation is possible. One filament forms a right-eye X-ray focal point 15 on the rotating anode, and the other filament forms a left-eye X-ray focal point 17 at another position on the rotating anode. The distance between the two focal points 15 and 17 is determined according to the parallax.

The X-ray high voltage device 11 is constructed so as to boost the commercial alternating current and alternately apply it to two filaments at a frequency of 60 Hz, for example. The configuration of the X-ray high voltage device 11 will be described later.

Image Intensifier (II)
19 is arranged so as to face the X-ray tube 13 with the subject in between, and converts the X-ray image transmitted through the subject into an optical image.
The TV camera 21 captures an optical image output from the image intensifier 19 at a frame rate of 60 Hz in synchronization with X-ray exposure from the bifocals 15 and 17.

The TV camera 21 alternately outputs a right-eye image signal and a left-eye image signal at a frame rate of 60 Hz. These right-eye image signals and left-eye image signals are
Through the analog-digital converter (A / D) 23, X-ray radiation from the two focal points 15 and 17, and the front-stage changeover switch 25 that performs a switching operation at a rate of 60 Hz in synchronization with the frame rate of the TV camera 21, the right eye Image signals for the right eye and image signals for the left eye are alternately supplied to the image memory for the left eye 29.

The right-eye image signal and the left-eye image signal alternately read from the image memories 27 and 29 at a rate of 60 Hz are monitored via a rear stage changeover switch 31 and a digital / analog converter (D / A) 33. Alternately displayed on 35. The displayed right-eye image and left-eye image are respectively observed by the observer's right eye and left eye through the liquid crystal shutter 37 and the polarizing glasses 39. Thereby, the observer can observe the stereoscopic image (recognize the stereoscopic structure of the object in his / her head).

FIG. 2 is a block diagram of the X-ray high voltage device 11 shown in FIG. First, the commercial AC of the commercial AC power supply 41 is rectified into a DC by the rectifier circuit 43. This direct current is converted into high-frequency alternating current by the inverter 45 and applied to the primary side of the step-up transformer 49 of the step-up / rectifier circuit 47. Boost
The rectifier circuit 47 is composed of this step-up transformer 49 and a Cockcroft-Walton circuit (CW circuit) 51. The high voltage that has been boosted by the step-up transformer 49 and the Cockcroft-Walton circuit 51 and full-wave rectified by the Cockcroft-Walton circuit 51 is passed through a high-voltage cable (not shown) to the anode of the X-ray tube 13 and the X-ray tube 13. Applied between the filaments.

Further, the X-ray high voltage apparatus 11 has an X-ray controller 53 as a control center thereof, an inverter control circuit 55 for controlling the inverter 45, and a variable current type heating power source 57 for supplying a filament current to the filament of the X-ray tube 13. It has a tube ammeter 59 for measuring the tube current and a filament current control circuit 61 for controlling the output (filament current) of the heating power source 57.

The inverter control circuit 55 is configured as a logical sum circuit, and is supplied with three control signals from the X-ray controller 53, that is, an inverter frequency signal 63, a pulse control signal 65, and an exposure control signal 67, and the logical sum of these signals is supplied. Is supplied to the inverter 45.

Next, the operation of this embodiment will be described. (Pulse control) The present invention relates to pulse control of X-ray exposure, that is, control relating to the timing of X-ray pulse exposure, the pulse width of the X-ray pulse, the exposure cycle, and the exposure interval (pause period). One of the features is that it is performed on the primary side of the step-up transformer 49. As described above, the inverter control circuit 55 is supplied with the inverter frequency signal 63, the pulse control signal 65, and the exposure control signal 67 from the X-ray controller 53. Then, the inverter control signal 69 as the logical sum of these is supplied from the inverter control circuit 55 to the inverter 45.

As shown in FIG. 3, the inverter frequency signal 63 is a high frequency signal having a frequency of 20 KHz and a duty ratio of 50%, for example. The pulse control signal 65 is, for example, a pulse train having a frequency of 10 Hz, a pulse width of 15 ms, and a duty ratio of 15%. Exposure control signal 67
Is a signal which is changed to "H" level only during a period in which the operator operates a console (not shown) to keep the stereo see-through button ON.

By supplying the inverter control signal 69 as the logical sum of these three signals to the inverter 45, an AC voltage of 20 is supplied to the primary side of the step-up transformer 49.
High frequency of KHz, applied continuously for 15ms,
After that, the cycle of being paused for a period of 85 ms is continuously repeated while the stereo see-through button is in the ON state. As a result, a high-voltage secondary voltage similar to the primary voltage waveform is generated on the secondary side of the step-up transformer 49, boosted by the Cockcroft-Walton circuit 51, and further full-wave rectified. This rectified high DC voltage is X
It is applied between the anode of the X-ray tube 13 and the filament of the X-ray tube 13.

Thus, under the condition (pulse width 15 ms, DUTY 15%) according to the inverter control signal 69, X
From the X-ray tube 13, 8 X-ray pulses with a pulse width of 15 ms
Irradiation is repeated at a cycle of 100 ms including a rest period of 5 ms. Since the intensity of X-rays is proportional to the square of the tube voltage, when the tube voltage is OFF, the X-rays are also OFF.
It will be in a state (a non-exposure dormant state). Therefore,
By applying a tube voltage having the same pulse width as the pulse X-ray desired to be generated to the X-ray tube as described above, a pulse X-ray having a desired pulse width can be generated.

Although the above description is based on the ideal case where there is no induced voltage, in reality, (a) an induced voltage is generated when the load of the inverter 45 is "L" and OFF. (B) There is a stray capacitance in the high-voltage cable that connects the booster / rectifier circuit 47 and the X-ray tube 13, (c) the high-voltage output part, specifically, the Cockcroft-Walton circuit 51 has a capacitor. For that reason, it takes time for the fall of the X-ray.
However, this is because (a) make the high-voltage cable as short as possible (it naturally becomes short in a small-sized portable X-ray diagnostic apparatus), and (b) Cockcroft-Walton circuit 51.
By reducing the capacity of the capacitor to the necessary minimum, the fall time can be shortened to the extent that it does not hinder stereoscopic vision. Specifically, if (A) is set to 50 to 60 cm and (A) is set to about 1000 pF, it is possible to sufficiently suppress the fall time to about 5 ms, and the pulse X of about 15 ms required for stereoscopic fluoroscopy. It is quite possible to generate lines.

Further, although the Cockcroft-Walton circuit 51 is used for the step-up / rectifier circuit 47, the Cockcroft-Walton circuit 51 uses a step-up transformer only to increase the voltage to a desired voltage. The amount of voltage drop is large. Therefore, the fall of the X-ray pulse becomes faster as a result, which is suitable for a stereoscopic fluoroscopic device that needs to generate the X-ray pulse.

If the above-mentioned method is used, pulse control of X-rays can be performed on the primary side of the step-up transformer 49 for tube voltage. Therefore, it is necessary to make the switching elements for pulse control compatible with high voltage. In addition, since it does not require a large amount of insulating oil, as a result, the device is extremely small and lightweight. As shown in FIG. 4, the housing of the X-ray high-voltage device 11 that also serves as the stand of the C-arm 20, It is possible to realize a portable stereo-compatible X-ray diagnostic apparatus provided with the casters 71.
In addition, because of the small size, two X
It is also possible to mount an X-ray high voltage device having a ray tube and an independent control system. When such an X-ray high-voltage generator is mounted, at least one of the tube voltage, the tube current, and the pulse width of the left and right X-rays can be individually adjusted on the left and right to be different on the left and right. This will be described later. (Tube Current Control) As is well known, the filament heating current for heating the filament of the X-ray tube 3 is the sum of the tube current and the filament current. Moreover, the tube current is determined by the filament temperature. That is, the control of the tube current is realized by adjusting the filament temperature by the filament current.

In the above description, the pulse X-ray is generated with a desired pulse width of, for example, about 15 ms by turning on / off the tube voltage. However, when stereoscopic fluoroscopy is performed, in addition to the pulse width of the pulse X-ray, The magnitude of the tube current is also a very important item. Here, the magnitude of the tube current is determined by the filament temperature, but it is very difficult to raise and lower the filament temperature instantaneously, so that the filament current is synchronized with ON / OFF of the tube voltage as in the conventional case. When turned ON / OFF, there is a sufficient possibility that the tube voltage will be turned OFF before the filament is heated to the desired temperature, and as a result, the pulse X-ray is generated with the desired tube current (desired X-ray intensity). A situation may occur in which it is not possible to emit radiation. In order to cope with such a situation, in the present invention, (i) heating is performed in advance, and (filament) the filament current is kept flowing during the pause period of the X-ray pulse so that the filament temperature does not decrease during the pause period. The control of, is the principle of the higher concept. Here, three types of operation modes corresponding to such a principle are provided, and will be described in order below. (First Operation Mode) The first operation mode corresponds to both the above principles (i) and (ro), and controls the filament current by using a sample and hold circuit (controls the tube current). To). In this case, the sample / hold circuit is included in the filament current control circuit 61.

As shown in FIG. 5A, the filament current supplied from the heating power source 57 to the filament during the feedback control period of, for example, 14 ms from the start of the pulse X-ray irradiation to the end of the irradiation, for example, is: For example, so-called feedback control is performed by the filament current control circuit 61 based on the effective value of the tube current measured by the tube ammeter 59 according to the feedback table in which the tube current and the feedback value (filament current) are associated with each other. Done. That is, the feedback control is started based on the actual tube current in synchronism with the start of the pulse X-ray irradiation, and continues until immediately before the end of the pulse X-ray irradiation.

The tube current at the end of the feedback control period is held in the sample / hold circuit of the filament current control circuit 61. In the period from the end of the feedback control period to the start of the next pulse X-ray exposure (86 ms), including the pulse X-ray rest period (85 ms), the filament current is converted into the held tube current in the feedback table. The corresponding ampere is continuously fed to the filament.

In the first operation mode, the filament current control circuit 61 needs to recognize the pulse X-ray exposure period and the rest period. This is, for example, in the filament current control circuit 61. Of the three signals output from 53 to the inverter control circuit 45,
The pulse control signal 65 and the radiation control signal 67 may be taken in and recognized based on the morale of these two signals, or other methods may be used.

When the feedback control is continued during the rest period without holding the actual tube current at the end of the feedback control period, the value of the tube current is "0".
Since the feedback current is applied to the feedback level, the filament current is applied at the maximum amperage during the rest period, which causes a problem of filament overheating, and the tube current of the pulse X-ray to be generated next time. Unnecessarily large, the next pulse X
The problem that the rays are exposed with higher X-ray intensity,
The filament breakage occurs. However, such a situation does not occur in the first operation mode.

However, in the first operation mode, as shown in FIG.
As shown in (b), when the tube current is unstable, the tube current of the pulse X-ray generated next is not stable, which is a minus side. This problem is likely to occur when the X-ray exposure is stopped before the feedback control enters the stable period, that is, when the pulse width is very short. The following second mode of operation can address this issue. (Second Operation Mode) The second operation mode also corresponds to both the principles of (i) and (ro), and in this mode, feedback control is not performed, that is, regardless of the tube current, The filament current is continuously supplied to the filament at a constant value over the entire period of the fluoroscopic period including both the pulse X-ray exposure period and the rest period, that is, asynchronously with ON / OFF of the pulse X-ray. Is the method.

As shown in FIG. 6, during stereo fluoroscopy, the filament current has a certain voltage value or current value, for example, X-ray condition, regardless of the pulse X-ray exposure period and the rest period. The optimum value of the filament current corresponding to the set X-ray condition is continuously supplied to the filament in accordance with the table in which the optimum value of the filament current is associated with the optimum value of the filament current, and thus the filament is continuously heated (or kept warm). It (Third mode of operation) The filament is a heat source,
Since the resistance is not always constant, in the second operation mode, the tube current value immediately after the start of stereoscopic fluoroscopy is different from that immediately before the end, that is, the resistance becomes lower immediately before the end and the current easily flows. It is possible that there is a risk of overheating the filament.

As shown in FIG. 7, the pulse X-ray exposure period is a feedback control period, and the filament current supplied from the heating power source 57 to the filament corresponds to, for example, a tube current and a feedback value (filament current). Tube ammeter 5 according to the feedback table
The so-called feedback control adjusted by the filament current control circuit 61 is performed based on the effective value of the tube current measured in 9.

In the rest period, a constant filament current is continuously supplied to the filament as in the second operation mode. By the third operation mode, the filament current is feedback-controlled while the actual tube current value is monitored during the X-ray exposure period, the heating state of the filament is adjusted, and the tube current can be suitably controlled. During the period, a constant filament current is continuously supplied to the filament to continuously heat (or keep warm) the filament.
can do.

Next, a method of attaching the X-ray tube 13 to the C arm 20 will be described. FIG. 8 shows a positional relationship between an operator who performs an operation, an examinee (patient), and a portable stereo-compatible X-ray diagnostic apparatus according to the present invention under stereoscopic fluoroscopy. The X-ray tube 13 is fixed to one end of the C-arm 20 in a state in which the array direction of the two focal points 15 and 17 (direction of the line connecting the two focal points 15 and 17) is parallel to the C-arm 20. In the operation, the installation position and orientation of the C-arm 20 with respect to the subject, and the position where the operator stands are uniquely determined depending on the treated site. For example, in most cases, such as a limb fracture operation, an X-ray tube is used. 13 two foci 15, 17
The arrangement direction of C and the direction of the C arm 20 coincide with each other. This is a positional relationship that enables stereoscopic viewing while securing a working space for the operator, that is, with such a positional relationship, X
The arrangement direction of the two focal points 15 and 17 of the line tube 13, the parallax direction of the operator (the direction of the line connecting both eyes) and the display direction of the monitor 13 (the direction of the line connecting the image centers of the left and right eyes) are made to coincide with each other. be able to. If the X-ray tube 13 has two focal points 15 and 17,
If the array direction of the operator does not match the parallax direction of the operator, for example, they are orthogonal to each other, the operator's parallax direction is substantially the same as the array of the right-eye image and the left-eye image displayed on the monitor 35. The image is misaligned by 90 °, and the operator cannot combine both images, resulting in a double appearance. Alternatively, when the orientation of the treated region viewed by the operator does not match the orientation of the left and right images on the monitor 35, the operation cannot be smoothly performed.

By fixing the X-ray tube 13 to the C-arm 20 in this way, a rotating mechanism, a sliding mechanism, etc. of the X-ray tube 13 are not required, and the size and weight can be reduced accordingly. Further, if the X-ray tube 13 is fixed to the C-arm 20, the standing position and the direction of the operator are limited with respect to the direction of the C-arm 20 (the direction of bifocal point) from the viewpoint of stereoscopic vision, but most operations are performed. Is possible with such a layout, and also
Such a layout can reduce the installation space of the device and the working space of the operator. Therefore, it is suitable for a portable X-ray diagnostic apparatus.

FIG. 9 shows a state of diseased limb surgery as an example in which the X-ray transmission attenuation amount is extremely different between the X-ray path from the right eye focus and the X-ray path from the left eye focus. There is. FIG. 10 is a block diagram of a main part of a stereo-compatible X-ray diagnostic apparatus corresponding to that at least one of the tube voltage, the tube current, and the X-ray pulse width can be individually set on the left and right. An operation panel 87 is connected to the CPU 81 via a control bus 83 and a panel interface 85. The panel 87 is provided with right X-ray condition setting means 89, right X-ray condition display means 91, left X-ray condition setting means 93, and left X-ray condition display means 95. X-ray tube 13L for the right eye having one focus and X-ray tube 13 for the left eye having one focus
Equipped with two X-ray tubes with R, these X-ray tubes for the right eye 1
The X-ray high-voltage devices 11L and 11R respectively corresponding to the 3L and the left-eye X-ray tube 13R are connected to the CPU 81 via the high-voltage control means 97 and the control bus 83.

Here, for convenience of explanation, the left and right X-ray tubes 13 are provided.
It is assumed that the X-ray conditions of L and 13R, that is, the tube voltage, the tube current, and the X-ray pulse width are initially set to be the same. The operator instructs the right X-ray condition setting means 89 to change at least one of the tube voltage, the tube current, and the X-ray pulse width of the right X-ray tube 13L. The CPU 81 recognizes the changed X-ray condition via the panel interface 85 and displays it on the right X-ray condition display means 91. Further, the CPU 81 instructs the high voltage control means 97 to change the right X-ray condition. The high voltage control means 97 controls the X-ray high voltage device 11L on the right side. X
The line high-voltage device 11L uses the right X-ray tube 1L so that X-rays are emitted from the right X-ray tube 13L under the changed X-ray conditions.
Drive 3L. The same applies to changing the X-ray condition on the left side.

In this way, at least one of the tube voltage, the tube current, and the X-ray pulse width can be adjusted separately for the X-ray for the right eye and the X-ray for the left eye. Even when the left and right X-ray attenuation amounts are extremely different, the left and right images can be adjusted to have the same image quality, and easy stereoscopic viewing is possible. This is important for a portable X-ray diagnostic apparatus which is often used in an emergency. The present invention can be implemented with various modifications without being limited to the above embodiments.

[0044]

According to the present invention, the following effects are exhibited. X-ray pulse width and timing control of exposure are
It is performed on the primary side of the step-up transformer. Therefore, this control element does not need to be compatible with high voltage, and a large amount of insulating oil is not required, so that it is possible to realize downsizing and weight saving, which can contribute to portability of the X-ray diagnostic apparatus.

The filament current is continuously supplied to the filament of the X-ray tube even during the rest period of the X-ray irradiation, and the filament is maintained in the heated state. Therefore,
There is no need to wait for the filament to heat up,
X-rays are emitted in synchronism with ON / OFF of the tube voltage.

By fixing the X-ray tube to the C arm,
The rotation mechanism and slide mechanism of the X-ray tube are unnecessary, and the size and weight can be reduced accordingly. Further, if the X-ray tube is fixed to the C-arm, the standing position and the orientation of the operator are restricted with respect to the orientation of the C-arm (bifocal orientation) from the viewpoint of stereoscopic vision. In addition, such a layout can reduce the installation space of the device and the working space of the operator.
Therefore, it is suitable for a portable X-ray diagnostic apparatus.

At least one of the tube voltage, the tube current, and the X-ray pulse width can be adjusted separately by the right-eye X-ray generation means and the left-eye X-ray generation means. Even when the left and right X-ray attenuation amounts are extremely different, the left and right images can be adjusted to have the same image quality, and easy stereoscopic viewing is possible. This is important for a portable X-ray diagnostic apparatus which is often used in an emergency.

As described above, since the X-ray diagnostic apparatus is portable and can be freely moved to a necessary place, it is possible to perform a diagnosis by stereoscopic observation on the spot without moving the subject in an emergency, etc. You can have surgery.

[Brief description of drawings]

FIG. 1 is a block diagram of an X-ray diagnostic apparatus according to an embodiment of the present invention.

FIG. 2 is a block diagram of the X-ray high voltage device in FIG.

FIG. 3 is a diagram showing input / output signals of the inverter control circuit of FIG.

FIG. 4 is an external view of the X-ray diagnostic apparatus in FIG.

5 is an explanatory diagram of a first mode of filament current control by the filament current control circuit of FIG.

FIG. 6 is an explanatory diagram of a second mode of filament current control by the filament current control circuit of FIG.

7 is an explanatory diagram of a third mode of filament current control by the filament current control circuit of FIG.

FIG. 8 is a diagram showing a relationship between a C arm and two focal points of an X-ray tube.

FIG. 9 is a diagram showing an example in which the X-ray transmission attenuation is extremely different between X-ray paths from the left and right focal points.

FIG. 10 is a block diagram of a system in which the tube voltage, the tube current, and the pulse width can be individually adjusted on the left and right.

FIG. 11 is an external view of a conventional stereo-compatible X-ray diagnostic apparatus.

[Explanation of symbols]

 11 ... X-ray high-voltage device, 13 ... X-ray tube, 15 ... Focus for right eye, 17 ... Focus for left eye, 19 ... Image intensifier, 20 ... C arm, 21 ... TV camera, 23 ... Analog-digital converter, 25 ... front-stage changeover switch, 27 ... right-eye image memory, 29 ... left-eye image memory, 31 ... rear-stage changeover switch, 33 ... digital-analog converter, 35 ... monitor, 37 ... liquid crystal shutter, 39 ... deflection glasses, 41 ... commercial AC power supply 43 ... Rectifier circuit, 45 ... Inverter, 47 ... Booster / rectifier circuit, 49 ... Booster transformer, 51 ... Cockcroft-Walton circuit, 53 ... X-ray controller, 55 ... Inverter control circuit, 57 ... Heating power supply, 59 ... Tube current Meter, 61 ... Filament current control circuit, 63 ... Inverter frequency signal, 65 ... Pulse Control signal, 67 ... Exposure control signal, 69 ... Inverter control signal.

(72) Inventor Kozo Nakagawa 1385-1 Shimoishigami, Otawara-shi, Tochigi Toshiba Nasu factory (72) Inventor Masayuki Nishiki 1385-1 Shimoishi, Otawara, Tochigi Toshiba Nasu in the factory

Claims (8)

[Claims] 1. An X-ray diagnostic apparatus for exposing a X-ray by applying a high voltage boosted by a boosting transformer to an X-ray tube and generating an image based on the X-ray transmitted through a subject. An X-ray diagnostic apparatus characterized in that the voltage applied to the primary side of a transformer is controlled to control the pulse width of X-rays and the timing of exposure. 2. The X-ray diagnostic apparatus according to claim 1, wherein a Cockcroft-Walton circuit for boosting and full-wave rectification is provided on the secondary side of the boosting transformer. 3. An X-ray diagnostic apparatus that intermittently irradiates X-rays from an X-ray tube and repeatedly generates an image based on the X-rays that have passed through an object, during the rest period of the X-ray irradiation. An X-ray diagnostic apparatus, wherein a constant filament current is continuously supplied to the filament of the X-ray tube. 4. The predetermined period within the X-ray exposure period,
The filament current is adjusted according to the actual tube current of the X-ray tube, and during the period including the rest period after the predetermined period, the filament current is a value corresponding to the actual tube current at the end of the predetermined period. The X-ray diagnostic apparatus according to claim 3, wherein the X-ray diagnostic apparatus is fixed to the. 5. The X-ray diagnostic apparatus according to claim 3, wherein the predetermined filament current is continuously supplied during the X-ray exposure period. 6. The X-ray diagnostic apparatus according to claim 3, wherein during the X-ray exposure period, the filament current is adjusted according to an actual tube current of the X-ray tube. 7. A stereo-compatible bifocal X-ray tube is attached to one end of the C-arm, and means for imaging an X-ray transmitted through a subject is attached to the other end, and a line connecting the bifocals is the C-arm. An X-ray diagnostic apparatus, wherein the X-ray tube is fixed to the C arm so as to be parallel to the arm. 8. An X-ray diagnostic apparatus having stereo-compatible right-eye X-ray generating means and left-eye X-ray generating means, wherein at least one of a tube voltage, a tube current, and an X-ray pulse width is used for the right-eye X-ray. An X-ray diagnostic apparatus, wherein the X-ray diagnostic means can be individually adjusted with respect to the X-ray generating means and the X-ray generating means for the left eye.