JP2012129087A - X-ray diagnostic device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an X-ray diagnostic device the running cost of which can be reduced by limiting the capacity of a power supply facility required for the X-ray diagnostic device using a battery, when a commercial power supply and a battery power supply are used while being switched.SOLUTION: The X-ray diagnostic device comprises high voltage generation means, a first power supply, a battery, and power supply switching means. The high voltage generation means applies a high voltage to an X-ray tube in order to generate X-rays. The power supply switching means supplies the high voltage generation means with power from the first power supply or power from the battery while switching so that power is supplied from the first power supply upon receiving an instruction of fluoroscopy, and supplies power from the battery upon receiving an instruction of radiography.

Description

  Embodiments described herein relate generally to an X-ray diagnostic apparatus having high voltage generation means for generating X-rays by applying a high voltage to an X-ray tube.

  As a conventional X-ray diagnostic apparatus, there is one that supplies a high voltage to an X-ray tube based on electric power supplied from a battery (for example, Patent Document 1).

  When a battery is used as a power source for generating X-rays, the power supply capacity of the battery is small, so that it has been used only for low-power X-ray diagnostic apparatuses such as mobile X-ray apparatuses.

  With the recent progress in battery technology, the battery performance has been improved and the life has been extended, and it has become possible to use it as a power source for generating X-rays such as a normal X-ray fluoroscopy device as an X-ray power source.

JP 2003-10167 A

  However, when using a battery as a power source for generating X-rays, switching between commercial power and battery power has the advantage of being used in areas where power supply conditions are poor or during power outages. The cost increase due to the addition of the battery could not be covered.

  This embodiment solves the above problem, and when using a battery and switching between a commercial power source and a battery power source, the capacity of the power supply facility required for the X-ray diagnostic apparatus is suppressed, and the running of the apparatus is reduced. An object is to provide an X-ray diagnostic apparatus that can be suppressed.

  In order to solve the above-described problem, an X-ray diagnostic apparatus according to an embodiment includes a high voltage generating unit, a first power source, a battery, and a power source switching unit, and the high voltage generating unit includes a high voltage in the X-ray tube. When the X-ray fluoroscopic instruction is received, the power supply switching means supplies the power from the first power source to the high voltage generating means and receives the X-ray imaging instruction. Then, the power from the first power supply and the power from the battery are switched and supplied to the high voltage generating means so that the power from the battery is supplied to the high voltage generating means.

It is a block diagram which shows a part of structure of the X-ray diagnostic apparatus which concerns on 1st embodiment. It is a block diagram which shows a part of structure of the X-ray diagnostic apparatus which concerns on 2nd embodiment.

  Next, various embodiments of the X-ray diagnostic apparatus will be described with reference to the drawings.

[First embodiment]
First, a first embodiment of an X-ray diagnostic apparatus will be described with reference to FIG. FIG. 1 is a block diagram showing a part of the configuration of the X-ray diagnostic apparatus.

  The X-ray diagnostic apparatus includes an X-ray tube 1, a high voltage generating means 2, an X-ray control means 3, an inverter unit 4, a commercial power supply 5, a rectifying means 6, a battery device 7, a changeover switch 8, and an X-ray condition setting means 9. Have. The battery device 7 is an example of the battery of the present invention that supplies power to the inverter unit 4.

  The X-ray control means 3 has a switching control circuit 12. The battery device 7 includes a plurality of (for example, about 4 to 25) battery units 10 and charge / discharge control means 11. The changeover switch 8 and the changeover control circuit 12 are an example of the power supply switching means of the present invention.

  High voltage generating means 2 is provided for applying a high voltage to the X-ray tube 1 to generate X-rays. The high voltage generating means 2 is connected to the inverter unit 4. The inverter unit 4 converts the power supplied from the commercial power supply 5, the rectifying means 6, or the battery device 7 to direct current to alternating current. The high voltage generating means 2 generates a high voltage by boosting the DC / AC converted power by a high voltage transformer (not shown).

  The X-ray control means 3 receives the X-ray irradiation conditions input by the X-ray condition setting means 9 and controls the high voltage generation means 2, the inverter unit 4, and the battery unit 10, respectively, to obtain desired X-rays. X-rays with irradiation conditions are generated. Here, the X-ray irradiation conditions include X-ray irradiation conditions (tube voltage, tube current, etc.) during X-ray fluoroscopy and X-ray imaging.

  The rectifier 6 converts alternating current from the commercial power source 5 into direct current. The rectifying means 6 outputs DC power to the inverter unit 4 via the changeover switch 8. The commercial power source 5 and the rectifying means 6 are an example of the first power source of the present invention.

  The X-ray control means 3 switches the changeover switch 8 so as to electrically connect the inverter unit 4 to the rectifying means 6 in response to the X-ray irradiation conditions during X-ray fluoroscopy input by the X-ray condition setting means 9. As a result, the DC power from the rectifying means 6 is supplied to the inverter unit 4. At this time, the charge / discharge control means 11 receives the charge instruction from the X-ray control means 3 and charges the battery unit 10. The battery unit 10 is charged during X-ray fluoroscopy so that it can be prepared for X-ray imaging performed after X-ray fluoroscopy.

  Further, the X-ray control means 3 receives the X-ray irradiation conditions at the time of X-ray imaging inputted by the X-ray condition setting means 9 and switches the switch 8 so as to electrically connect the inverter unit 4 to the battery device 7. Is switched to supply the DC power from the battery device 7 to the inverter unit 4. At this time, the charge / discharge control means 11 receives the discharge instruction from the X-ray control means 3 and discharges the battery unit 10. At this time, the charge / discharge control means 11 does not charge the battery unit 10. That is, the battery unit 10 is charged during operation including X-ray fluoroscopy except during X-ray imaging.

  As described above, power for generating X-rays is supplied from the commercial power supply 5, the rectifying means 6, or the battery device 7, and switching is performed by the changeover switch 8. The changeover switch 8 is controlled by the changeover control circuit 12 of the X-ray control means 3.

  Next, the operation of the power supply switching means including the changeover switch 8 and the changeover control circuit 12 will be described.

(X-ray fluoroscopy)
When receiving an X-ray fluoroscopic instruction from the X-ray control means 3, the switching control circuit 12 operates the changeover switch 8 so as to supply power from the first power supply (commercial power supply 5, rectifying means 6). When performing X-ray imaging, it operates to supply power from the battery device 7. As a result, the commercial power supply supplies power for generating X-rays only when performing X-ray fluoroscopy with relatively small power to be used, and the power supply capacity that is always connected may be small.

  When the X-ray is not generated by the electric power from the battery device 7, that is, when the changeover switch 8 is connected to the first power supply (commercial power supply 5, rectifying means 6), the charge / discharge control means 11 is always a battery. The unit 10 is charged. Since the power required for charging the battery unit 10 by the first power supply (commercial power supply 5 and rectifying means 6) may be smaller than the power required for X-ray imaging, it is always connected at this time. Similarly, the power supply capacity may be small as well. However, it is possible to generate X-rays with a small power supply capacity in both X-ray fluoroscopy and X-ray imaging.

(X-ray photography)
On the other hand, when receiving an X-ray imaging instruction from the X-ray control unit 3, the switching control circuit 12 operates the selector switch 8 so as to supply electric power from the battery device 7. Thereby, the same photographing output as the conventional one can be obtained.

[Second Embodiment]
Next, a second embodiment of the X-ray diagnostic apparatus will be described with reference to FIG. FIG. 2 is a block diagram showing a part of the configuration of the X-ray diagnostic apparatus as in FIG.

  Since the basic configuration of the X-ray diagnostic apparatus according to the second embodiment is the same as that of the first embodiment, description of the basic configuration is omitted, and a configuration different from the first embodiment will be described. .

  In addition to the X-ray diagnostic apparatus according to the first embodiment, the power transformer 13 connected from the commercial power source 5 for charging the plurality of battery units 10 of the battery device 7 and the output of the power transformer 13 are connected to the AC DC. The rectifying means 14 for conversion is connected to each other, and the output of the rectifying means 14 is connected to the battery device 7.

  The electric power of the commercial power source 5 stepped down by the power transformer 13 is supplied to the battery device 7 through the rectifier 14. The commercial power source 5, the power transformer 13 and the rectifier 14 are an example of the second power source of the present invention for charging the battery device 7. The charge / discharge control means 11 charges each battery unit 10 with power from the second power source.

  Further, the output of the battery device 7 is directly connected to the inverter unit 4 via a diode 15. Here, the output of the power transformer 13 is set so that the output voltage Vo of the first power supply (commercial power supply 5 and rectifier 6) and the output voltage Vb of the rectifier 14 always satisfy Vo> Vb. Although the output voltage of the battery device 7 is lower than the output voltage Vb of the rectifying means 14 due to the electrical resistance present in the battery device 7, the following description will be made assuming that the output voltage of the battery device 7 is also Vb.

  As described above, one of the reasons for Vo> Vb is that by increasing the output voltage Vo of the first power supply, even if the current I from the first power supply is small, X-ray irradiation and the battery device 7 can be charged, and even if the output voltage Vb of the battery device 7 is lowered, by connecting the battery units 10 in parallel, the current I from the battery device 7 is increased and X-ray imaging is performed. It is because it becomes possible to do.

  In the X-ray diagnostic apparatus configured as described above, the switching control circuit 12 electrically connects the first power supply (commercial power supply 5 and rectifying means 6) and the inverter unit 4 during fluoroscopy. The changeover switch 8a is switched to the on state. Thereby, X-rays are generated at the output of the first power source (commercial power source 5, rectifier 6). Here, there is another reason why Vo> Vb. Since it is Vo> Vb, it becomes possible to prevent the current from flowing back from the first power source (commercial power source 5, rectifier 6) to the battery device 7 by turning off the diode 15. . The changeover switch 8a is an example of the first changeover means of the present invention. The diode 15 is an example of the second switching means of the present invention.

  On the other hand, at the time of X-ray imaging, the switching control circuit 12 switches the selector switch 8 to an off state so as not to electrically connect the first power source (commercial power source 5 and rectifying means 6) and the inverter unit 4. Thereby, the diode 15 is turned on, the battery device 7 and the inverter unit 4 are electrically connected, and X-rays are generated by the output of the battery device 7.

  Since the diode 15 is turned off when X-rays are generated by the output of the first power supply (commercial power supply 5 and rectifying means 6), the output of the battery device 7 is always directly connected to the inverter unit 4 via the diode 15. It becomes possible to do. In this case, the changeover switch 8 only needs to switch the power source on the plus side, and the power supply to be switched has a relatively small output under X-ray fluoroscopic conditions.

  According to such an embodiment, it is possible to use a small-capacity switch for switching between the commercial power source and the battery, and it is not necessary to switch the output for generating X-rays at the time of X-ray imaging. Reliability can be improved.

  According to the embodiment described above, when a battery used as a power source for generating X-rays is used, the capacity of power supply equipment necessary for the X-ray diagnostic apparatus can be suppressed, and the running cost of the apparatus can be reduced. In addition, it is possible to provide an X-ray diagnostic apparatus having improved quality and reliability while suppressing the introduction cost.

  In the second embodiment, the power supply transformer means 13 is used in the battery charging circuit. However, the power transformer means may be provided in the X-ray fluoroscopic circuit using the commercial power supply 5 to boost the voltage. Thereby, the same kind of structure as the X-ray diagnostic apparatus which concerns on 2nd embodiment is realizable.

  Although several embodiments of the present invention have been described, these embodiments are presented by way of example and are not intended to limit the scope of the invention. These novel embodiments can be implemented in various other forms, and various omissions, rewrites, and changes can be made without departing from the scope of the invention. These embodiments and modifications thereof are included in the scope and gist of the invention, and are included in the invention described in the claims and the equivalents thereof.

DESCRIPTION OF SYMBOLS 1 X-ray tube 2 High voltage generation means 3 X-ray control means 4 Inverter unit 5 Commercial power supply 6 Rectification means 7 Battery apparatus 8 Changeover switch 9 X-ray condition setting means 10 Battery unit 11 Charge / discharge control means 12 Switching control circuit 13 Power supply transformation Means 14 Rectifying means 15 Diode

Claims (4)

In an X-ray diagnostic apparatus having a high voltage generating means for applying a high voltage to an X-ray tube,
The first power supply,
Battery,
When an instruction for fluoroscopy is received, power from the first power source is supplied to the high voltage generation means, and when an instruction for X-ray imaging is received, power from the battery is supplied to the high voltage generation means. Power supply switching means for switching between the power from the first power source and the power from the battery so as to supply;
An X-ray diagnostic apparatus comprising: A second power source for charging the battery;
The X-ray diagnostic apparatus according to claim 1, wherein the power supply switching unit charges the battery with the second power supply when receiving an instruction for fluoroscopy.   The power supply switching means is switched on to electrically connect the first power supply and the high voltage generating means when receiving an X-ray fluoroscopic instruction, and receives an X-ray imaging instruction. The first switching means that is switched to the off state and the x-ray radiography instruction are switched to the off state so that the current from the first power source does not flow back to the battery when the x-ray fluoroscopic instruction is received. 3. The X-ray diagnostic apparatus according to claim 1, further comprising a second switching unit that is switched to an on state so as to electrically connect the battery and the high voltage generation unit. The second switching means is a diode;
The X-ray diagnostic apparatus according to claim 3, wherein the battery supplies a voltage lower than an output voltage of the first power supply to the high voltage generation unit through the diode.

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