JP2007151707A - X-ray computed tomography system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an X-ray computed tomography system which facilitates the maintenance and check operation of a power supply part by preventing the power supply part from wearing and corroding. <P>SOLUTION: The system is provided with: mechanical power supply means 301a, 301b, and 301c as a means to supply electric power to an X-ray tube 560 from a power source 1; and a signal transmission means, as a means for sending a detected signal to an image processing part 2 from the X-ray detection part 550, composed of a light emitting device 302a which is provided at a scanner rotation part to convert output vibration from the X-ray detection part 550 into light and a light receiving device 302b provided at a scanner fixation part to convert light into an electric signal. The system is provided with an electromagnetic induction power generation means 40, an electric transformer 541, and a rectifier 542. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to an X-ray CT apparatus provided with a continuously rotating scanner rotating unit, which can reduce the burden on power supply equipment mounted on the scanner and can easily improve maintenance and inspection of the power supply unit. It relates to possible X-ray CT apparatus.

  The X-ray CT apparatus irradiates a subject with a fan-shaped X-ray beam from an X-ray tube, detects X-rays transmitted through the subject with an X-ray detector disposed at a position facing the X-ray tube, The detected data is image-processed to obtain a tomographic image of the subject. The X-ray detector is composed of hundreds of detection element groups arranged in an arc shape, and is arranged to face the X-ray tube across the subject, corresponding to the number of detector elements. A number of radially distributed X-ray passages are formed, and the X-ray tube and the detector are integrated to rotate around the subject by at least 180 degrees to detect transmitted X-rays of the subject at certain angles. . This X-ray CT system has features such as “a wide range of scanning is possible in a short time” and “continuous data can be obtained in the body axis direction, which makes it possible to generate 3D images”. Also known as spiral scan, spiral scan is already popular.

  In order to realize this spiral scan, it is necessary to continuously rotate the scanner turntable. To that end, slip rings and brushes are used to continuously supply power to the X-ray tube mounted on the scanner turntable. A mechanical power supply mechanism is used.

Patent Document 1 is characterized in that an electric double layer capacitor or a polymer capacitor using a polymer material as a dielectric is mounted as a secondary battery in the scanner rotating unit and power is supplied to the X-ray tube. In addition, the power transmission means and the signal transmission means are worn or corroded by mechanical sliding contact with a slip ring and a brush by supplying power without contact by using a power transmission coil for the scanner fixing part and a plurality of power reception coils for the scanner rotation part. Is avoiding.
JP 2001-258874 A

  In the method disclosed in Patent Document 1, a capacitor element (an electric double layer capacitor and a polymer capacitor using a polymer material) mounted on a charged scanner rotating unit is disposed on the anode side and the cathode side of the X-ray tube. Although power is supplied, the energy is so large that it is technically difficult to realize with existing capacitors. For example, an apparatus that requires 60 kW with a scan time of 7 seconds requires an energy supply of 116.7 Wh. Currently, when using commercially available capacitors, it is necessary to configure a plurality of large capacitors in combination with series and parallel connections, and the power transmission coil and power reception coil that can sufficiently charge these capacitors will increase in size. The point was not considered.

  An object of the present invention is to provide an X-ray CT apparatus that prevents wear and corrosion of a power supply portion and facilitates maintenance and inspection of the power supply portion.

  An X-ray CT apparatus for achieving the above object detects an X-ray tube that emits X-rays and a transmitted X-ray dose distribution in which the X-rays emitted from the X-ray tube pass through the subject and outputs the detection signal. A scanner rotation unit that has an X-ray detection unit to amplify and rotates the X-ray tube and the X-ray detection unit facing each other around the subject, a high voltage generation unit that generates a high voltage, and the high voltage generation In an X-ray CT apparatus comprising a power supply means for supplying a high voltage from the scanner to the scanner rotation unit, the power supply means includes a magnetic body disposed on the periphery of the fixed frame of the scanner rotation unit, Electromagnetic induction power generation means comprising a winding disposed opposite to the magnetic body and disposed on a rotating frame of the scanner rotating portion and connected to the input side of the X-ray tube.

  According to the present invention, it is possible to improve the reliability of the entire apparatus by preventing wear and corrosion of the power supply portion and facilitating maintenance and inspection of the power supply means.

  The structure of the first embodiment of the X-ray CT apparatus according to the present invention will be described with reference to FIG.

  As shown in FIG. 1, an X-ray CT apparatus emits X-rays to a diagnosis site of a subject, detects the transmitted X-ray dose distribution, reconstructs a tomographic image, and displays it as an image. As shown, a power source 1, an anode rotation drive device 510 for an X-ray tube 560, a high voltage generation circuit 520, a filament heating circuit 530 for an X-ray tube 560, an X-ray detection unit 550, and an image processing unit 2 are provided. As a means for supplying power from the power source 1 to the X-ray tube 560, mechanical power supply means 301a, 301b, 301c, electromagnetic induction power generation means 40, and further, detection from the X-ray detection unit 550 to the image processing unit 2 Signal transmission by means of a light emitting element 302a for converting the output vibration from the X-ray detection unit 550 provided in the scanner rotating unit into light as a means for sending a signal and a light receiving element 302b for converting light provided in the scanner fixing unit into an electric signal Means.

  The power source 1 generates a DC voltage to be supplied to the anode rotation driving device 510, the high voltage generation circuit 520, and the filament heating circuit 530. In FIG. 1, a commercial AC power source 101 and a voltage of this AC power source are set to a desired voltage. It consists of two converter circuits 102 and 103 which convert to a DC voltage and smooth it. The commercial power source as the input power source of the power source 1 is a single-phase AC power source as an example, but this may be a three-phase AC power source, and the power source 1 can generate a DC voltage. For example, a battery may be used. The converter circuit 102 outputs a DC voltage such as 700 V required by the anode rotation driving device 510 in the scanner rotation unit 5 and the high voltage generation circuit 520. The converter circuit 103 outputs, for example, a DC voltage of 15 V as a power source to each control circuit that controls the anode rotation driving device 510, the high voltage generation circuit 520, and the filament heating circuit 530.

  The mechanical power supply means 301a, 301b, 301c smooth the DC voltage generated by the power source 1 of the scanner fixing unit by the smoothing capacitor 524 in the scanner rotating unit 5, and rotate the anode rotation driving device 510, the high voltage generating circuit 520, and the filament heating. It consists of a brush, a slip ring, etc. transmitted to the circuit 530 and utilizing mechanical sliding contact. The voltage generated by the power source 1 is a DC voltage in FIG. 1, but depending on the internal configuration of the power source 1, the anode rotation driving device 510, the high voltage generation circuit 520, and the filament heating circuit 530, or the previous stage of these circuits. In the case of having a converter that converts alternating current into direct current, an alternating voltage may be used. Furthermore, if AC voltage transmission is used, the mechanical power supply means 301a and 301b may be a non-contact type using an electromagnetic induction function in which a primary winding is provided on the scanner fixing portion and a secondary winding is provided on the scanner rotation portion. good. Further, in the voltage supply to the anode rotation driving device 510 and the high voltage generation circuit 520, the mechanical power supply means 301a and 301b are shared in order to supply the same voltage in FIG. In order to supply different voltages depending on the configuration, respective mechanical power supply means may be provided. Further, the power supply to each control circuit for controlling the anode rotation driving device 510, the high voltage generation circuit 520 and the filament heating circuit 530 transmitted by the mechanical power supply means 301c is a single voltage in FIG. However, a plurality of mechanical power supply means may be provided to supply different voltages. Alternatively, a control power supply circuit may be provided in the scanner rotation unit, and the voltage input from the mechanical power supply unit 301c may be converted into a different DC voltage.

  The electromagnetic induction power generation means 40 will be described in detail later in the main part of this patent. The electromagnetic induction power generation means 40 is arranged opposite to the magnetic body 401 and the ferromagnetic body 401 in which a plurality of polarities are arranged on the circumference of the scanner fixing portion. And an inductor 402 disposed on the rotation frame of the scanner rotation unit. The electromagnetic induction power generation means 40 generates an electromotive voltage by the rotation of the scanner, converts the AC voltage into a desired voltage by the transformer 541, and rectifies it by the rectifier 542. The rectified DC voltage has a voltage value slightly larger than the voltage transmitted by the mechanical power supply means 301a and 301b, and a current flows from the rectifier 542 to the smoothing capacitor and the capacitor 524. The smoothing capacitor 524 is composed of an electrolytic capacitor and smoothes the voltage.

  The X-ray tube anode rotation drive circuit 510 applies a three-phase AC voltage to the stator coil 561 of the X-ray tube anode rotation drive mechanism in order to reduce the addition of the anode target of the X-ray tube 560 during X-ray emission. It is a circuit for supplying. The DC voltage supplied from the smoothing capacitor 524 is converted into a three-phase AC voltage having a frequency set by the inverter circuit 511, which is supplied to the stator coil 561, and the anode of the X-ray tube 560 is rotated at a predetermined rotation. Rotate by number.

  The high voltage generation circuit 520 includes an inverter circuit 521, a high voltage transformer 522, and a high voltage rectifier 523. The inverter circuit 521 is an inverter circuit that receives the DC voltage supplied from the mechanical power supply means 301a and 301b. This is converted into high-frequency alternating current at 521 and boosted by a high-voltage transformer 522. The boosted AC voltage is converted to a DC high voltage by the high voltage rectifier 523, smoothed by the capacitor 524, the smoothed high voltage is applied to the X-ray tube 560, and X-rays are emitted from the X-ray tube 560.

  The filament heating circuit 530 supplies an X-ray tube filament for generating a required X-ray irradiation amount by passing a current (hereinafter referred to as a tube current) between the anode and the cathode of the X-ray tube. In the heating circuit, the inverter circuit 531 converts the DC voltage supplied from the smoothing capacitor 524 into a single-phase AC voltage having a predetermined frequency, and this voltage is applied to the filament of the X-ray tube 560 via the heating transformer 532. The filament is heated to a predetermined temperature.

The X-ray detection unit 550 includes a detector 551 that detects a transmitted X-ray distribution emitted from the X-ray tube 560 and transmitted through the subject, and a preamplifier 552 that amplifies a detection signal from the detector 551.
The signal transmission means by the light emitting element 302a and the light receiving element 302b for converting the light provided in the scanner fixing portion into an electric signal is similar to the mechanical power supply means 301a, 301b, 301c, and includes brushes and slip rings by mechanical sliding contact. The means used may be used.
The image processing unit 2 receives and processes the output signal from the X-ray detection unit 550, and reconstructs a tomographic image of the diagnosis region of the subject, and the output signal from the image processing device 201 And an image display device 202 for inputting and displaying a tomographic image.

As described above, the scanner rotation unit 5 includes the anode rotation drive circuit 510, the high voltage generation circuit 520, the filament heating circuit 530, the X-ray tube 560, and the X-ray detection unit 550. The tube 560 and the X-ray detection unit 550 face each other with the subject interposed therebetween and rotate around the subject.
The scanner rotation unit 5 has a rotation frame in which an opening for inserting a subject is formed at the center. The anode rotation drive circuit 510, the high voltage generation circuit 520, and the filament heating are provided on one side of the rotation frame. A circuit 530, an X-ray tube 560, and an X-ray detector 550 are mounted, and a light emitting element 302a for transmitting a detection signal is provided around the body of the rotating frame, and the scanner is fixed facing the light emitting element. The light receiving element 302b is provided in the frame, and the X-ray detection signal transmitted through the subject is transmitted to the image processing unit 2 by these.

  4 and 5 show a first embodiment of the electromagnetic induction power generation means 40 which is a main part of the present invention. 4 is a cross-sectional view showing the positional relationship among the subject insertion opening 51, the fixed frame 11, and the rotating frame 52 of the scanner. FIG. 5 is a front view of the electromagnetic induction power generation means 40 surrounded by the broken line in FIG. FIG.

First, the scanner rotation frame 52 is rotatably mounted by bearings 12a and 12b provided at a predetermined distance in the axial direction inside the fixed frame 11. On the periphery of the inner surface of the fixed frame 11, a plurality of magnetic bodies 401a, 401b, 401c are fixed and arranged so that different polarities are arranged. On the outer peripheral surface of the rotating frame 52, an inductor 402 having a winding wound around an iron core is disposed. The iron core of the inductor 402 has a horseshoe shape and is disposed so that both end faces thereof are spaced apart from the magnetic pole surfaces of the magnetic bodies 401a, 401b, 401c by a predetermined distance. By configuring the electromagnetic induction power generation means 40 as described above, a magnetic flux change occurs in the inductor 402 when the scanner rotates, and the winding of the inductor 402 in which an electromotive force is generated at both ends of the winding of the inductor 402 is shown in FIG. The converter circuit 541 shown in FIG. For example, if the scanner rotates once in 0.6 seconds and the magnetic poles of the permanent magnets arranged on the circumference with an opening diameter of 800 mm are arranged at intervals of 100 mm, the magnetic flux generated in the inductor 402 is 0.048 s. The size changes with the period. When the magnetic flux density of the permanent magnet is 1 T, the area where the magnetic flux of the inductor 402 interlinks is 1000 mm ² , and the number of turns is 240, the generated electromotive force can be obtained by the following equation.
Electromotive force =-(Number of turns)-(Magnetic flux linkage area)-(Change rate of magnetic flux density)
= -240 x 1000 x 10 ^-6 x (1 / 0.024)
= -10 V

  The AC voltage thus obtained can be converted to a desired voltage by the transformer 541, converted to a DC voltage by the rectifier 542, and electric power can be supplied via the smoothing capacitor 524. A plurality of inductors 402 may be arranged and connected in series or in parallel to supplement the power.

  6 and 7 show a second embodiment of the electromagnetic induction power generation means 40. FIG. FIG. 6 is a cross-sectional view showing the positional relationship among the object insertion opening 51 of the scanner, the fixed frame 11 and the rotary frame 52, and FIG. 7 shows the electromagnetic induction power generation means 40 surrounded by the broken line in FIG. FIG.

  The electromagnetic induction power generation means 40 in this embodiment follows the same principle as the first embodiment of the electromagnetic induction power generation means 40, but the scanner rotation frame 52 is separated by a predetermined distance in the axial direction inside the fixed frame 11. The bearings 12a and 12b are provided so as to be rotatable. A plurality of magnetic bodies 401a, 401b, 401c are fixed on the periphery of the side outer surface of the fixed frame 11, and are arranged so that different polarities are arranged. On the inner side surface of the rotating frame 52, an inductor 402 having a winding wound around an iron core is disposed. The inductor 402 has a horseshoe shape and is disposed so that both end faces thereof are opposed to the magnetic pole surfaces of the magnetic bodies 401a, 401b, and 401c by a predetermined distance. By configuring the electromagnetic induction power generation means 40 as described above, when the scanner rotates, a change in magnetic flux occurs in the inductor 402, and an electromotive force is generated at both ends of the winding of the inductor 402. The AC voltage thus obtained can be converted to a desired voltage by the transformer 541, converted to a DC voltage by the rectifier 542, and electric power can be supplied via the smoothing capacitor 524.

  In the second embodiment of the electromagnetic induction power generation means 40, since the magnetic body is arranged on the outer side of the rotating shaft as compared with the first embodiment of the electromagnetic induction power generation means 40, the centrifugal force increases and the structure of the entire apparatus However, the outer shape of the magnetic cores 401a, 401b, 401c and the inductor 402 can be easily formed in a straight line or a plane.

  The structure of the second embodiment of the X-ray CT apparatus according to the present invention will be described with reference to FIG. In the first embodiment of the X-ray CT apparatus, the electromagnetic induction power generation means 40, the transformer 541, and the rectifier 542 are connected to the anode drive circuit 510, the high voltage generation circuit 520, and the filament heating circuit 530 through the smoothing capacitor 512. On the other hand, in the second embodiment of the X-ray CT apparatus, the electromagnetic induction power generation means 40, the transformer 541, and the rectifier 542 are connected only to the anode drive circuit 510 and the filament heating circuit 530 via the smoothing capacitor 512. Yes. The power source 1 includes a converter 104 in the commercial power source 101 and supplies power to the anode drive circuit 510 and the filament heating circuit 530 separately from the high voltage generation circuit 520 via the mechanical power supply means 301d and 301e.

  Hereinafter, the configuration and operation of each unit different from the first embodiment of the X-ray CT apparatus will be described. The power supply 1 has a converter 104 connected to the commercial power supply 101, generates a DC voltage, and smoothes the DC voltage with a smoothing capacitor 512 via mechanical power supply means 301d and 301e. The electromagnetic induction power generation means 40 generates an electromotive voltage by the rotation of the scanner, converts the AC voltage into a desired voltage by the transformer 541, and rectifies it by the rectifier 542. The rectified DC voltage has a voltage value slightly larger than the voltage transmitted by the mechanical power supply means 301d and 301e, and a current flows from the rectifier 542 to the smoothing capacitor 512.

The anode driving circuit 510 converts the DC voltage supplied from the smoothing capacitor 512 into a three-phase AC voltage having a frequency set by the inverter circuit 511, and supplies the same to the stator coil 561 so that the X-ray tube 560 The anode is rotated at a predetermined rotational speed.
The filament heating circuit 530 converts the DC voltage supplied from the smoothing capacitor 512 into a single-phase AC voltage having a predetermined frequency by the inverter circuit 531, and applies this voltage to the filament of the X-ray tube 560 via the heating transformer 532. The filament is heated to a predetermined temperature.

  In the second embodiment of the X-ray CT apparatus, since the electromotive force generated by the electromagnetic induction power generation means 40 can be made smaller than that of the first embodiment of the X-ray CT apparatus, the electromagnetic induction power generation means and 40, the transformer 541, and the rectifier 542 are provided. Can be downsized.

The structure of the third embodiment of the X-ray CT apparatus according to the invention will be described with reference to FIG. In this embodiment, the first and second embodiments of the X-ray CT apparatus are combined, and two separate electromotive forces are generated by the electromagnetic induction power generation means 41, and one AC voltage is transformed. The power can be supplied through the smoothing capacitor 524 after being converted to a desired voltage by the rectifier 541a and converted to a DC voltage by the rectifier 542a. The other AC voltage generated by the electromagnetic induction power generation means 41 can be converted into a desired voltage by the transformer 541b, converted to a DC voltage by the rectifier 542b, and power can be supplied via the smoothing capacitor 512. .
Therefore, the electromagnetic induction power generation means 41 in this embodiment has a different form from the electromagnetic induction power generation means 40 in the first and second embodiments. Hereinafter, a specific structure of the electromagnetic induction power generation means 41 will be described with reference to the drawings.

  8 and 9 show a first embodiment of the electromagnetic induction power generation means 41. FIG. 8 is a cross-sectional view showing the positional relationship among the subject insertion opening 51, the fixed frame 11 and the rotating frame 52 of the scanner, and FIG. 9 is a front view of the electromagnetic induction power generation means 41 surrounded by a broken line in FIG. FIG. First, the scanner rotation frame 52 is rotatably mounted by bearings 12a and 12b provided at a predetermined distance in the axial direction inside the fixed frame 11. On the periphery of the inner surface of the fixed frame 11, a plurality of magnetic bodies 401a, 401b, 401c are fixed and arranged so that different polarities are arranged. On the outer peripheral surface of the rotating frame 52, inductors 402a and 402b in which two iron cores are wound are arranged. The iron cores of the inductors 402a and 403b have a horseshoe shape and are arranged so that both end faces thereof are separated from the magnetic pole surfaces of the magnetic bodies 401a, 401b, and 401c by a predetermined distance. By configuring the electromagnetic induction power generation means 41 as described above, when the scanner rotates, a change in magnetic flux occurs in the inductors 402a and 402b, and an electromotive force is generated at each end of each winding of the inductors 402a and 402b. The AC voltage thus obtained is converted to a desired voltage by the transformer 541, converted to a DC voltage by the rectifier 542, and electric power can be supplied via the smoothing capacitors 512 and 524.

  10 and 11 show a second embodiment of the electromagnetic induction power generation means 41. FIG. 10 is a cross-sectional view showing the positional relationship among the subject insertion opening 51, the fixed frame 11, and the rotating frame 52 of the scanner. FIG. 11 is a front view of the electromagnetic induction power generation means 41 surrounded by a broken line in FIG. FIG. The electromagnetic induction power generation means 41 in this embodiment follows the same principle as in the first embodiment, but the scanner rotation frame 52 is a bearing 12a provided at a predetermined distance in the axial direction inside the fixed frame 11. , 12b is rotatably mounted. A plurality of magnetic bodies 401a, 401b, 401c are fixed on the periphery of the side outer surface of the fixed frame 11, and are arranged so that different polarities are arranged. Inductors 402a and 403b each having a winding wound around an iron core are disposed on the inner surface of the rotating frame 52. The inductors 402a and 403b are horseshoe-shaped, and are arranged so that both end faces thereof are separated from the magnetic pole surfaces of the magnetic bodies 401a, 401b, and 401c by a predetermined distance. By configuring the electromagnetic induction power generation means 41 as described above, when the scanner rotates, a change in magnetic flux occurs in the inductors 402a and 403b, and an electromotive force is generated at both ends of the windings of the inductors 402a and 403b. The AC voltage thus obtained is converted to a desired voltage by the transformer 541, converted to a DC voltage by the rectifier 542, and electric power can be supplied via the smoothing capacitors 512 and 524.

In the second embodiment of the electromagnetic induction power generation means 41, since the magnetic body is arranged on the outer side of the rotating shaft as compared with the first embodiment of the electromagnetic induction power generation means 41, the centrifugal force is increased and the structure of the entire apparatus is increased. However, the outer shape of the iron cores of the magnetic bodies 401a, 401b, 401c and the inductors 402a, 403b can be easily formed in a straight line or a plane.
In the embodiment, the inductor 402a and the inductor 402b can be arranged with respect to the rotation axis, so that there is a specific effect that the rotation balance is good.

  As described above, as can be seen from the first, second, and third embodiments of the X-ray CT apparatus, electromagnetic induction power generation means 40 and 41, smoothing capacitors 512 and 524, and a circuit for generating X-rays, Various forms of connection combinations of the anode drive circuit 510, the high voltage generation circuit 520, and the filament heating circuit 430 can be considered. These can be appropriately determined according to the scale of the electromagnetic induction power generation means 40, 41 depending on the external dimensions of the scanner and the form of the mechanical power supply means 301a to 301e.

  The structure of the fourth embodiment of the X-ray CT apparatus according to the present invention will be described. This embodiment is basically a modification of the first, second, and third embodiments of the present X-ray CT apparatus, and the smoothing capacitors 512, 524 have an electric function as a battery. Use a double layer capacitor. FIG. 12 shows a replacement circuit for the smoothing capacitors 412 and 524 when an electric double layer capacitor is used. The DC voltage supplied from the mechanical power supply means 301a, 301b or 301d, 301e and the converter circuits 511, 541 is charged to the electric double layer capacitor 601 through the series connection body of the current controller 611 and the diode 612. . The current controller 611 controls the current until the electric double layer capacitor 601 reaches a specified voltage.

  In this case, the mechanical power supply means 301a, 301b, 301d, 301e do not need to be a conventional slip ring system. The slip ring method is a method in which electric power is always supplied regardless of whether the scanner is stationary or rotating. However, in this embodiment, any method may be used as long as the electric double layer capacitor 601 is charged only when the scanner is stationary. It suffices to provide power supply means at a specific position on each of the scanner fixed frame side and the rotary frame side. During the rotation of the scanner, in addition to the electric power charged in the electric double layer capacitor 601, it operates to generate X-rays with the electric power generated by the electromagnetic induction power generation means 40 and 41.

Furthermore, the mechanical power supply means 301c is similarly applied to the power supply to the control circuit for controlling the anode rotation driving device 510, the high voltage generation circuit 520, and the filament heating circuit 530 transmitted by the mechanical power supply means 301c. Is a power supply means provided at a specific position on each of the scanner fixed frame side and the rotary frame side as described above, and the circuit shown in FIG. Further, the electromagnetic induction power generation means 40 is configured to be connected to the circuit shown in FIG. 12 for supplying power to the control circuit. As a result, power can be supplied to the scanner rotation frame in a completely non-contact state during scanner rotation.
The electric double layer capacitor 601 in the present embodiment is not limited to this, and may be any capacitor having a high energy density that serves as a battery, such as a polymer capacitor using a polymer material.

  As described above, this embodiment can be said to be a form that can most reduce the wear and corrosion of the power supply means as compared with the first, second, and third embodiments.

1 shows a first embodiment of an X-ray CT apparatus according to the present invention. 2 shows a second embodiment of an X-ray CT apparatus according to the present invention. 3 shows a third embodiment of an X-ray CT apparatus according to the present invention. A first embodiment of the electromagnetic induction power generation means 40. The figure which looked at the 1st Example of the electromagnetic induction electric power generation means 40 from the front. 2 shows a second embodiment of the electromagnetic induction power generation means 40. FIG. The figure which looked at the 2nd Example of the electromagnetic induction electric power generation means 40 from the upper part. 1 shows a first embodiment of electromagnetic induction power generation means 41. FIG. FIG. 3 is a front view of a first embodiment of the electromagnetic induction power generation means 41. 2 shows a second embodiment of the electromagnetic induction power generation means 41. FIG. The figure which looked at the 2nd Example of the electromagnetic induction electric power generation means 41 from the front. The electric double layer capacitor charging circuit in the fourth embodiment of the X-ray CT apparatus.

Explanation of symbols

  1 Power supply, 2 Image processing unit, 5 Scanner rotating unit, 11 Scanner fixed frame, 12a, 12b bearing, 40, 41 Electromagnetic induction generator, 51 Scanner object insertion opening, 52 Scanner rotating frame, 101 Commercial AC power supply, 102, 103, 104, 511, 541 converter circuit, 201 image processing device, 202 image display device, 301a, 301b, 301c, 301d, 301e mechanical power supply means, 302a light emitting element, 302b light receiving element, 401, 401a, 401b, 401c Magnetic body, 402, 402a, 402b Inductor, 510 Anode drive circuit, 511, 521, 531 Inverter circuit, 512, 524 Smoothing capacitor, 520 High voltage generation circuit, 522 High voltage transformer, 523 High voltage rectifier , 530 Filament heating circuit, 532 heating transformer, 541 transformer, 542 rectifier, 550 X-ray detector, 551 detector, 552 preamplifier, 560 X-ray tube, 561 X-ray tube stator coil, 601 electric double layer capacitor, 611 current controller, 612 Diode

Claims (3)

  An X-ray tube that emits X-rays and an X-ray detector that detects a transmitted X-ray dose distribution in which X-rays emitted from the X-ray tube pass through the subject and amplifies the detection signal. And a X-ray detection unit facing each other and rotating around the subject, a scanner rotation unit, a high voltage generation unit that generates a high voltage, and a high voltage from the high voltage generation unit is supplied to the scanner rotation unit In the X-ray CT apparatus provided with the power supply means, the power supply means is disposed on the circumference of the fixed frame of the scanner rotating portion, and is disposed to face the magnetic body and the scanner. An X-ray CT apparatus comprising: an electromagnetic induction power generation unit including a winding disposed on a rotating frame of a rotating unit and connected to an input side of the X-ray tube.   The X-ray CT apparatus according to claim 1, further comprising a secondary battery that supplies the power supply unit.   The electromagnetic induction power generation means is composed of a magnetic body disposed on the circumference of the fixed frame of the scanner rotating portion and a magnetic body provided with a winding disposed on the rotating frame of the scanner rotating portion. 3. The X-ray CT apparatus according to claim 1, wherein electric power is supplied to the X-ray tube by an electromotive force generated by a change in magnetic flux generated inside the winding.

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