JP2006288726A - Medical x-ray radiographing device and x-ray detector used for the same - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide medical X-ray radiographing device for panoramic shot and CT imaging in combination which does not increase costs while utilizing characteristic of an electric imaging means sufficiently, and to provide an X-ray detector. <P>SOLUTION: The medical X-ray radiographing device A is provided with: a support body 3b of a rotation member; the rotation member 6 supported rotatably by the support body 3b; an X-ray generator 9 provided at one section of the rotation member 6; and the X-ray detector 10 provided at another section of the rotation member 6 so as to oppose the X-ray generator 9. To the X-ray detector 10, two kinds of electric imaging means 14a and 14b of different shapes can be mounted. One 14b of the kinds of electric imaging means 14a and 14b is long and narrow, and the other 14a has a flat shape expanding in a two-dimensional direction. According to an X-ray imaging mode, two kinds of the electric imaging means 14a and 14b can be selected and used. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a medical X-ray imaging apparatus, and more particularly to an X-ray imaging apparatus used for dental, otolaryngological and other medical purposes capable of panoramic imaging and CT imaging.

  As an example of the medical X-ray imaging apparatus, an X-ray generator is provided at one end of the swivel arm, and an X-ray detection unit is provided at the other end, and the trajectory along which the X-ray beam follows the shape of the dental arch ( It has both a panoramic imaging function that performs tomography while swirling while drawing an envelope) and a CT imaging function (computer tomography) that performs tomography of the target tooth while rotating the swivel arm around the target tooth. Dental X-ray imaging apparatuses have been put into practical use. And as an X-ray detection part, in addition to the conventional analog imaging means by X-ray film, electrical imaging means, such as CCD, came to be used. In the case of the latter electrical imaging means, linear scanning is possible, so even in the case of panoramic photography, the X-ray detection unit may be a vertically long and small area, and the obtained image is a digital image. It can be used arbitrarily, and it can be applied in many ways, such as being able to display captured images on a monitor TV in real time.

In Patent Document 1, an analog film cassette and a CCD or MOS digital sensor cassette can be mounted on the X-ray detector, and an analog or digital tomographic image is selectively acquired by selectively switching between them. A medical X-ray tomography apparatus as described above is disclosed. Patent Document 2 discloses an X-ray imaging apparatus capable of performing panoramic imaging and CT imaging and using a two-dimensional digital sensor such as a MOS as an X-ray detection unit.
Japanese Patent Laid-Open No. 9-135829 JP-A-10-225455

  Thus, in the medical X-ray tomography apparatus of Patent Document 1, the X-ray detection unit uses both an analog film cassette and a digital sensor cassette, and an electrical imaging means, that is, a CCD or MOS The two-dimensional digital sensor such as the above is used, and the two types of digital sensors having different shapes are used properly, so that it is not configured to cope with panoramic imaging and CT imaging. It was hard to say that it could be fully utilized. The X-ray imaging apparatus disclosed in Patent Document 2 can handle panoramic imaging and CT imaging using a single two-dimensional digital sensor such as a MOS. It needs a big thing to be able to cope with CT photography and also cephalometric photography, MOS is very expensive at present, and there is a problem in terms of economy, so it has not yet been put into practical use. It is a fact.

  The present invention has been made in view of the above. A medical X-ray imaging apparatus for panoramic imaging and CT imaging that does not increase the cost while fully utilizing the characteristics of the electrical imaging means, and X-ray detection used therefor It is in providing a vessel.

  The medical X-ray imaging apparatus according to the invention of claim 1 includes a support member for a turning member, a turning member that is turnably supported by the support member, and an X-ray generator provided at one part of the turning member. A medical X-ray imaging apparatus comprising an X-ray detector provided at the other part of the swivel member so as to face the X-ray generator, wherein the X-ray detector is an electric device having two different shapes An imaging unit can be attached, and one of the two types of electrical imaging unit has an elongated shape, and the other has a planar shape extending in a two-dimensional direction. It is characterized in that a selective imaging means is selectively used.

  The two types of electrical imaging means can be formed on one side of a single substrate as in the invention of claim 2. In this case, as in the invention of claim 3, the two types of electrical imaging means can be selectively used by allowing the single substrate to be displaced with respect to the X-ray detection unit. Alternatively, as in the invention of claim 4, by making the directing direction of the X-ray beam with respect to the X-ray detector of the X-ray generator variable, the two types of electrical imaging means can be selectively used. It is possible to

  Further, the two types of electrical imaging means are formed on both surfaces of a single substrate as in the invention of claim 5, and the two types of electrical imaging means are selectively used by inverting the substrates. Or, as in the invention of claim 6, is formed on a peripheral surface of a columnar base that is rotatably attached to the X-ray detection unit, and the columnar base is rotated around the axis. Thus, the two types of electrical imaging means can be selected and used. Further, as in the invention of claim 7, each of the two sheets is formed on two separate substrates. It is also desirable to adopt the two types of electrical imaging means by attaching both and / or one of the substrates to the X-ray detector so as to be detachable or displaceable. Is done.

  In any one of the inventions, as in the invention of the eighth aspect, the one electrical imaging means is composed of a CCD and the other electrical imaging means is composed of a MOS, or the invention of claim 9 As described above, both of the one electrical imaging means and the other electrical imaging means can be made of MOS. According to a tenth aspect of the present invention, the X-ray imaging mode is a panoramic imaging mode and a CT imaging mode, and the one electrical imaging unit corresponds to the panoramic imaging mode, and the other electrical imaging unit. It is desirable that corresponds to the CT imaging mode. In this case, as in the eleventh aspect of the present invention, the X-ray imaging mode further includes a cephalometric imaging mode, wherein at least one of the electric imaging means is detachable from the X-ray detection unit, The electric imaging means can be attached to and detached from the X-ray detection unit for the cephalometric imaging mode, and the shape thereof can be formed so that it can also be used for the cephalometric imaging mode.

  Further, in any one of the inventions, as in the invention of the twelfth aspect, it is desirable to include a control means for performing selection setting of the X-ray imaging mode based on selection information of the two types of electrical imaging means. Then, as in the thirteenth aspect of the present invention, the control means controls the turning of the turning member based on the turning pattern corresponding to the selected X-ray imaging mode, the X-ray generation control in the X-ray generator, and the selection. Further, the drive control of the electrical imaging means is performed, and further, as in the invention of claim 14, the primary slit and / or X on the X-ray generator side according to the selected X-ray imaging mode. It is desirable to control so that the secondary slits on the line detection unit side are switched to suitable ones.

  An X-ray detector according to a fifteenth aspect of the invention includes a support member for a turning member, a turning member that is turnably supported by the support member, an X-ray generator provided at a part of the turning member, and a turning member. An X-ray detector attached to the X-ray detection unit of a medical X-ray imaging apparatus including an X-ray detection unit provided at another part of the member so as to face the X-ray generator. A substrate and two types of electrical imaging means formed on the plate surface of the substrate, one of the two types of electrical imaging means being elongated and the other being a plane extending in the two-dimensional direction It is characterized by being shaped. Also in the X-ray detector of the present invention, as in the invention of claim 16, the one electrical imaging means is composed of a CCD and the other electrical imaging means is composed of a MOS, or As in the seventeenth aspect of the present invention, both of the one electrical imaging means and the other electrical imaging means can be made of MOS.

  The MOS in the above invention is a concept including a CMOS. In addition to the CCD or the MOS, a thin film transistor (TFT) or an X-ray solid element can be used as the electrical imaging means.

  According to the first aspect of the present invention, two types of electrical imaging means having different shapes can be attached to the X-ray detection unit, and one is an elongated shape and the other is a planar shape extending in the two-dimensional direction. Therefore, as in the invention of claim 9, if one of them is made to correspond to the panoramic imaging mode and the other is made to correspond to the CT imaging mode, panoramic imaging can be performed by linear scanning, and the image Therefore, it is possible to obtain a very useful photographed image. Further, since the CT imaging is not required to be as large as the left side, as in the invention of claim 8 (invention of claim 16), one electrical imaging means is composed of CCD and the other electrical The imaging means is made of MOS, or both the one electric imaging means and the other electric imaging means are made of MOS as in the invention of claim 9 (invention of claim 17). As a result, the electrical imaging means as a whole is not increased and the cost is not increased. In addition, since the image processing can be performed in real time by using the CCD, the image processing is efficient and a good linear scan image can be obtained. In addition, by adopting a MOS that can capture moving images, it is possible to arbitrarily aim at the object to be imaged by shifting the overlapping portion, for example, forming a tomographic image or a panoramic image of an arbitrary part included in the dental arch. . As a result, the characteristics of the electrical image pickup means as a digital image forming medium are fully exhibited, and multifaceted application of the photographed image becomes possible.

  In addition, if two types of electrical imaging means or X-ray detectors are configured as in the invention of any one of claims 2 to 7 or 15, the electrical imaging means can be selected and used easily. Further, if identification means for specifying each is provided, information on which one is selected and set is associated with the X-ray imaging mode such as panoramic imaging or CT imaging. If such a control means is provided, the selection setting of the X-ray imaging mode based on this selection information can be easily performed. If this control means also performs the control as in the invention of claim 13 or claim 14, panoramic imaging or CT imaging using the selection information of the two types of electrical imaging means as a key. It is possible to automatically perform the operation control of each mechanism unit or the like necessary for performing the operation based on a preset sequence.

  Further, as in the eleventh aspect of the present invention, if the X-ray imaging mode includes the cephalometric imaging mode and one of the electric imaging means can be used for both the panoramic imaging mode and the cephalometric imaging mode, one device is provided. Thus, X-ray imaging can be performed in the panoramic imaging mode, CT imaging mode, and cephalometric imaging mode, and a space-saving and multi-faceted medical X-ray imaging apparatus can be realized without increasing the cost.

  Hereinafter, the best mode of the present invention will be described with reference to the drawings. FIG. 1 is a front view of a dental X-ray imaging apparatus as an example of a medical X-ray imaging apparatus of the present invention, FIG. 2 is a left side view thereof, FIG. 3 is an overall configuration diagram of the apparatus, and FIG. FIG. 5 is a drive circuit diagram of an X-ray detection sensor using MOS, FIG. 6 is a flowchart of an imaging mode using the X-ray imaging apparatus, and FIG. 7 is a diagram for explaining the details of the X generator. Is a longitudinal sectional view, and (b) is a perspective view of the main part. 8 is a longitudinal sectional view showing an example of the X-ray detection unit, FIG. 9 is an exploded perspective view of the main part of the X-ray detection unit, FIG. 10 is a longitudinal sectional view showing another example of the X-ray detection unit, and FIG. FIG. 12 is an exploded perspective view of the main part of the X-ray detection unit, and FIGS. 13A and 13B are views of the X-ray detector when the X-ray detector is fixed. It is explanatory drawing which shows the aspect of the positional relationship of a line generator and an X-ray detection part.

  The dental X-ray imaging apparatus A shown in FIGS. 1 to 3 is capable of panoramic imaging, CT imaging, and cephalometric imaging, and a column 2 is erected on a base 1 installed on a floor surface. The main body 3 is supported on the support column 2 through an elevating mechanism 3a (see FIG. 3) so as to be movable up and down. A C-shaped (in a side view) body frame (support) 3b of the main body 3 is fixedly provided with a horizontal cephalo arm 4, and a cephalo photographing unit 5 is provided at the tip thereof. The cephalometric imaging unit 5 includes a patient head holding portion (including ear restraints) 5b and a patient head holding portion 5b sandwiched between a lower surface of a base plate 5a that is rotatable around a vertical axis. The primary slit 5c and the Cephalo X-ray detector 5d are arranged.

  An inverted concave revolving arm (a revolving member) 6 is suspended on the upper side of the main body frame 3b, and the revolving arm 6 includes a rotary table 7 and an XY table 8 (see FIG. 3) built in the main body frame 3b. ) Enables horizontal turning or two-dimensional movement in a horizontal plane area. The swivel member 6 is not limited to the swivel arm 6 having the shape as shown in the figure, but may be a ring shape, or may have a function of tilting up and down without being limited to the horizontal movement as described above. An X-ray generator 9 is disposed at one end of the swivel arm 6, and an X-ray detector 10 is disposed at the other end so as to face the X-ray generator 9. Between the X-ray generator 9 and the X-ray detection unit 10, a head holding unit 11 that holds the head of the patient P is formed, and a patient positioning member such as a chin rest 11a is provided. The chin rest 11a can be moved up and down or tilted and positioned according to the patient's body shape. By configuring the upper and lower chin rests 11a to be movable in this way, for example, adjusting the inclination of the irradiation line with respect to the horizontal plane for each imaging region, the temporomandibular joint located above, and the lower jaw tip located below, It is also possible to adjust so that the site separated from the top and bottom is well positioned at the center of the irradiation field. Reference numeral 11b denotes a handle held by a patient standing on the base 1a, and 11c denotes a mirror.

  Here, the configuration of the head holding unit 11 will be described in detail. In the example of FIG. 1, the head holding unit 11 is displaced up and down with respect to the support column 2 according to the patient's physique. In the head holding part 11, a part for holding the patient by the chin rest 11 a and the part for moving up and down with respect to the support column 2 are integrally formed. Therefore, the X-ray generator 9 and the X-ray detection unit 10 move up and down together with the head holding unit 11. However, the above-described portion for holding the patient and the portion that moves up and down with respect to the column 2 accompanied by the raising and lowering of the X-ray generator 9 and the X-ray detection unit 10 are configured separately. However, they may be displaced independently of each other. Moreover, you may comprise so that the X-ray generator 9 may be displaced with respect to the part holding a patient. Japanese Patent Application Laid-Open No. 7-275240 related to the applicant's application discloses an example in which the part that moves up and down with respect to the above-mentioned support column 2 and the part that holds the patient are configured separately, and the part that holds the patient. On the other hand, an example in which the X-ray generator 9 is configured to move up and down is disclosed.

  In Japanese Patent Laid-Open No. 7-275240, a portion corresponding to the above-described portion for holding a patient is referred to as a “patient frame”, and a portion corresponding to a portion that moves up and down relative to the support column 2 is referred to as a “lifting body”. Is to widen the imageable region, and for example, to adjust the inclination of the irradiation line with respect to the horizontal plane for each imaging region, like the temporomandibular joint located above and the lower jaw tip located below, It is to adjust so that the part separated vertically is positioned in the center of the irradiation field. X-ray generation for a configuration in which the chin rest 11a can be moved up and down or tilted, a configuration in which the above-described patient holding portion and a portion to be displaced up and down with respect to the support column 2 are separated, and a patient holding portion You may make it possible to perform a more delicate adjustment combining the structure which the apparatus 9 moved up and down.

  As shown in FIG. 7, the X-ray generator 9 includes an X-ray tube 9a, an inner case 9b incorporating the X-ray tube 9a, and an outer case 9c. One end of the swivel arm 6 is interposed via a vertical support shaft 9d. It is supported by. The vertical support shaft 9d can be rotated by a motor 9e and a gear 9f, whereby the X-ray generator 9 can be rotated (oscillated) around the axis of the vertical support shaft 9d. A support block 13 for the primary slit plate 12 is fixed to the X-ray emission port of the X-ray tube 9a, and the primary slit plate 12 is attached to the support block 13 so as to be laterally movable.

  That is, a slit drive motor 13a is fixed to one side of the support block 13, and a base portion of a slit support rod 13c is screwed to a screw shaft 13b that is connected to the output shaft of the motor 13a. In addition, a tip end portion of a guide bar 13d supported by the support block 13 so as to be slidable in the same direction as the screw shaft 13b is fixed to the slit support rod 13c. Accordingly, the shaft 13b of the screw shaft 13b accompanying the drive of the motor 13a causes the slit support rod 13c to be screwed / retracted from side to side. The slit plate 12 is fixed to the front end of the slit support rod 13c, and the upper and lower sides of the slit plate 12 are sandwiched by a plurality of rollers 13e attached to the support block 13, whereby the slit support rod 13c The lateral movement of the slit plate 12 accompanying the left and right screwing and screwing is smoothly performed.

  The slit plate 12 includes a substantially rectangular (approximately 120 × 120 mm) CT imaging slit 12a, a vertically long (approximately 150 × 6 mm) panoramic imaging slit 12b, and a further vertically (approximately 225 × 6 mm) cephalometric imaging slit 12c. Are formed in parallel. Accordingly, by driving the motor 13a in accordance with the X-ray imaging mode, these slits 12a, 12b, and 12c are positioned at the X-ray emission port. When the cephalometric mode is set, the position of the cephalometric slit 12c is set and the X-ray generator 9 is swung by driving the motor 9e so that the cephalometric unit 5 of the cephalometric unit 5 is driven. It is positioned so that the X-ray beam is directed to the line detector 5d.

  In the X-ray detection unit 10 shown in FIG. 3, a sensor holder 15 for holding an X-ray detection sensor substrate 14 in which two types of X-ray detection sensors (electrical imaging means) 14a and 14b described later are formed is turned. The sensor holder 15 is attached to the other end of the arm 6 so as to be laterally movable. The sensor holder 15 can be laterally moved by a motor 15a. Output connectors (not shown) corresponding to the X-ray detection sensors 14 a and 14 b are formed on the X-ray detection sensor substrate 14, and when the X-ray detection unit 10 is attached via the sensor holder 15, The line detection unit 10 is connected to an input unit (not shown) formed in the line detection unit 10.

  Further, on the front side of the X-ray detection sensor substrate 14, a secondary slit plate 16 in which two types of slits 16a and 16b are formed is disposed as will be described later. The secondary slit plate 16 is driven by a motor 16c. It is possible to move horizontally. Accordingly, one of the X-ray detection sensors 14a and 14b is selected and set by driving the motor 15a, and according to the type of the sensors 14a and 14b by driving the motor 16c, that is, according to the X-ray imaging mode. One of the slits 16a and 16b is selected and set. Such an X-ray detection sensor substrate 14 and the secondary slit plate 16 can be detachably attached to the X-ray detection unit 10 as a cassette unit 100 as shown in FIG. It is also possible to detachably mount the cephalometric X-ray detection unit 5d of the cephalometric imaging unit 5 so that it can be used in combination.

  Next, operation control of the dental X-ray imaging apparatus A will be described with reference to FIGS. 3 and 4 are for explaining panoramic imaging and CT imaging, and the cephalo imaging is omitted. When shooting in the panorama shooting mode, when the panorama shooting mode is selected on the operation panel (input means) 17, a vertically long X-ray detection sensor 14b composed of a CCD on the X-ray detection sensor substrate 14 is loaded as described later. The motor 15a is driven and positioned so as to be positioned in the X-ray beam irradiation field. Further, as will be described later, a vertically long slit 16b formed in the secondary slit plate 16 drives the motor 16c and is positioned on the front side of the X-ray detection sensor 14b. The drive control of the motor 15a is performed by the X-ray detection sensor switching control circuit 15b, and the drive control of the motor 16c is performed by the secondary slit control circuit 16d. An IC chip (not shown) for identifying the two types of X-ray detection sensors 14a and 14b is attached to the X-ray detection sensor substrate 14, and the detected information is sent from the X-ray detection sensor type determination circuit 18 to the CPU 19. It is input and it is determined which X-ray detection sensor 14a, 14b has been set.

  In the X-ray generator 9, the motor 13a is driven and controlled by the primary slit control circuit 12d, and the panoramic imaging slit 12b is set at the X-ray emission port. Then, by operating the operation panel 17, the main body elevation control motor 3b of the elevating mechanism 3a is driven to set the main body 3 at an appropriate position according to the body shape of the patient P and to adjust the height or inclination degree of the chin rest 11a. This is done by the chin rest position control circuit 11b. Thus, when a photographing switch (not shown) is turned on on the operation panel 17, the arm rotation control motor 7a of the rotary table 7, the X-axis control motor 8a and the Y-axis control motor 8b of the XY table 8 are driven by the motor. Controlled by the control circuit 20, the swivel arm 6 is horizontally swung and moved around the dental arch of the patient P so that the X-ray beam draws a predetermined envelope trajectory. During the operation of the swivel arm 6, the X-ray control circuit 90 controls the X-ray tube 9a of the X-ray generator 9, and the X-ray beam is emitted and transmitted through the primary slit 12b and irradiated to the patient P. The X-rays that have passed through the secondary slit 16b are detected by the X-ray detection sensor 14b, and full jaw tomography of the dental arch is performed. The turning angle of the turning arm 6 is detected by the angle sensor 21.

  The image signal output from the X-ray detection sensor 14 b is output to the video memory 24, converted into a digital signal by the signal processing unit 22, and then calculated into a tomographic image along an arbitrary tomographic plane by the image reconstruction unit 23. It is processed and displayed by an image display unit 26 such as a cathode ray tube (abbreviated as “CRT”) and used for various diagnoses. Since the image reconstruction means 23 is specifically composed of an image reconstruction program, it may be processed using the central processing unit (CPU) 19 or a separate computer may be used.

  A work memory 27 necessary for signal processing is connected to the CPU 19, and an operation panel which is an input means including a panel switch for selecting an imaging mode and an X-ray irradiation switch for controlling on / off of X-ray irradiation. 17 is connected. The CPU 19 also includes the motor drive circuit 20, the primary slit control circuit 12d, the secondary slit control circuit 16d, the X-ray control circuit 90 for controlling the X-ray generator 9, and the control circuits 20, 12d, 16d, 90. Clock circuits 28 for outputting clock signals for synchronizing the control operations are connected to each other. The X-ray control circuit 90 can feedback-control the X-ray irradiation amount to the subject (patient P) based on the signal imaged by the X-ray detection sensor 14b made of a CCD. The control means 29 includes these CPU 19, frame memory 31, work memory 27, operation panel 17, motor drive circuit 20, primary slit control circuit 12 d, secondary slit control circuit 16 d, X-ray control circuit 90 and clock circuit 28. Is configured.

  When performing imaging in the CT imaging mode, if the CT imaging mode is selected on the operation panel (input means) 17, a rectangular X-ray detection sensor 14a made of MOS on the X-ray detection sensor substrate 14 is provided as described later. The motor 15a is driven so as to be positioned in the X-ray beam irradiation field. Further, as will be described later, a rectangular slit 16a formed in the secondary slit plate 16 is positioned on the front side of the X-ray detection sensor 14a by driving of the motor 16c. Based on the output information from the X-ray detection sensor type determination circuit 18 as described above, the CPU 19 determines which of the X-ray detection sensors 14 a and 14 b has been set.

  In the X-ray generator 9, the motor 13a is driven and controlled by the primary slit control circuit 12d, and the CT imaging slit 12a is set at the X-ray emission port. Then, the patient P is positioned by the operation of the operation panel 17 and the target region, here, the target tooth is indicated on the display (not shown) of the operation panel 17 to control the motor drive control circuit 20. Then, the X-axis control motor 8a and the Y-axis control motor 8b of the XY table 8 are driven, and the turning center of the turning arm 6 is set to coincide with the center of the target tooth. Such position setting is not limited to the horizontal movement of the swivel arm 6, but a chair capable of two-dimensional horizontal movement is installed on the base 1, and the patient is seated on the chair, and then the chair is horizontally placed. It is also possible to do this by moving it.

  Thus, when a photographing switch (not shown) is turned on on the operation panel 17, the arm rotation control motor 7a of the rotary table 7 is controlled by the motor drive control circuit 20, and the turning arm 6 is centered on the target tooth as described above. Turn around the turning center that matches During the turning operation of the turning arm 6, the output of the X-ray tube 9a of the X-ray generator 9 is controlled by the X-ray control circuit 90, the X-ray beam is radiated and transmitted through the primary slit 12a, and the patient P X-rays that are irradiated on the target tooth and passed through the secondary slit 16a are detected and photographed by the X-ray detection sensor 14a. This imaging is performed over 360 ° around the target tooth, and the CT images are sequentially taken into the video memory 24. In the above description, the image is taken over 360 [deg.], But it is sufficient that the image is taken over 180 [deg.] Necessary for the construction of the CT image.

  As shown in the drive circuit diagram of FIG. 5, the X-ray detection sensor 14a made of MOS has a plurality of photodiodes PD serving as light receiving pixels arranged in a matrix of m rows × n columns, and each photodiode PD. The junction capacitor C1 is connected in parallel, and the read switch SW is connected in series. The gate of the switch SW is connected to the address selection circuit SL, and the photodiode PD to be read is selected based on the signal from the CPU 21. In the above configuration, panoramic imaging can also be configured by using the X-ray detection sensor 14a made of MOS. In this case, the panoramic imaging slit 12a shown in FIG. 7 is used to capture an X-ray beam as a slit beam. According to this configuration, the panorama can be photographed by the X-ray detection sensor 14a made of MOS or the vertically long X-ray detection sensor 14b made of CCD, and can be arbitrarily selected.

  The output side of the switch SW is commonly connected in units of columns and is input to the operational amplifier Q1 constituting the current-voltage conversion circuit. The output of the operational amplifier Q1 is sampled by the sample hold circuit S / H. Each sample and hold circuit is connected to a switch SWb that is opened and closed by an m-stage shift register SR. As each open / close switch SWb sequentially opens and closes, the sampled signal is transferred onto the video line as a time-series signal and output to the guide buffer BF. If such a MOS is used, a moving image can be obtained. Therefore, by shifting the overlapped portion, the target location can be aimed arbitrarily, and the accuracy of CT imaging can be improved. Note that the X-ray detection sensor 14b can also be configured by a MOS to perform panoramic imaging, and the above characteristic peculiar to the MOS is also exhibited in the panoramic imaging.

  FIG. 6 is a flowchart of an imaging mode using the dental X-ray imaging apparatus. In step S1, the X-ray detection sensor type determination circuit 18 determines selection of the X-ray detection sensors 14a and 14b. In S2, it is determined whether or not the sensor is the MOS sensor, that is, the X-ray detection sensor 14a. If NO, the apparatus is set to the CCD sensor mode, that is, the panoramic imaging mode in Step S3. If preparation is completed in step S4, panoramic shooting is executed. If it is determined in step S2 that the sensor is a MOS sensor, in step S6, the apparatus is set to the MOS sensor mode, that is, the CT imaging mode. If preparation is completed in step S7, CT imaging is executed.

  8 and 9 show another embodiment of an electrical imaging means, that is, an X-ray detector attached to the X-ray detection unit 10. The X-ray detection unit 10 includes a secondary slit plate 16. An example in which an X-ray detection sensor substrate 14 in which two types of X-ray detection sensors 14a and 14b similar to the above are formed, that is, an X-ray detector 140 is detachably attached to a sensor holder 15 integrated with Show. The X-ray detection sensors 14a and 14b are each composed of a rectangular (about 120 × 120 mm) MOS and the latter is a vertically long (about 150 × 6 mm) CCD, but both can be composed of MOS. The sensor holder 15 is slidably supported on the end of the swivel arm 6 via a slide mechanism 15b composed of a guide body and a slide member, and can be moved laterally by a motor 15a. In the secondary slit plate 16, two types of secondary slits 16a and 16b are formed in the same manner as described above, and each corresponds to the X-ray detection sensors 14a and 14b.

  Output connectors (not shown) corresponding to the X-ray detection sensors 14 a and 14 b are formed on the X-ray detection sensor substrate 14, and when the X-ray detection unit 10 is attached via the sensor holder 15, The point which is made to be connected to the input part (not shown) formed in the line detection part 10 is the same as the above. The X-ray detector 140 shown on the upper side of FIG. 9 has the two types of X-ray detection sensors 14a and 14b formed on one side of the X-ray detection sensor substrate 14, and the X-ray detection shown on the lower side thereof. The instrument 140 is formed by forming the two types of X-ray detection sensors 14a and 14b on both sides of the X-ray detection sensor substrate 14, respectively. In the latter example, the front and back are reversed and mounted in accordance with a desired X-ray imaging mode. Therefore, in order to distinguish the front and back, an identifier 14c made of an IC chip or the like is attached to the plate surface of the X-ray detection sensor substrate 14, and when the sensor holder 15 is mounted, the identifier 14c is attached to the sensor holder 15. The identification is made by the provided detection means (not shown).

  Since such an X-ray detector 140 is detachable from the sensor holder 15, it is convenient for maintenance such as repair and replacement. Further, if the X-ray detection sensor 14b is a vertically long sensor of about 225 × 6 mm, it can be used for cephalometric imaging by being mounted on the cephalometric X-ray detection unit 5d of the cephalometric imaging unit 5. Since the execution mode of each X-ray imaging mode of panoramic imaging and CT imaging using the X-ray detector 140 is the same as described above, the description thereof is omitted here.

  The X-ray detector 140 shown in FIG. 10 has two types of X-ray detection sensors 14a and 14b similar to those described above on the peripheral surface of the columnar substrate 30 supported at the end of the swivel arm 6 so as to be rotatable around the vertical axis. Shows an example where is formed. Reference numeral 30a denotes a support shaft for supporting the columnar substrate 30 so as to be rotatable around a vertical axis as indicated by an arrow in the figure. In addition, secondary slit plates 16 and 16 having secondary slits 16a and 16b respectively corresponding to the X-ray detection sensors 14a and 14b are fixed to the columnar base 30. The columnar substrate 30 can be rotated by driving a motor with a separate motor, or by manual operation by an operator. By this turning operation, the position of any X-ray detection sensor 14a, 14b and secondary slit 16a, 16b is set so as to face the X-ray generator 9, and the same X-ray imaging mode as described above is executed. .

  Needless to say, it is desirable to appropriately assign an identifier (not shown) to the columnar base 30 so that the set state can be discriminated. Needless to say, the output of detection output signals (imaging data) of the X-ray detection sensors 14a and 14b is made by electrical connection (not shown) from the columnar base 30 through the inside of the turning arm 6. Again, since the execution mode of each X-ray imaging mode is the same as described above, the description thereof is omitted.

  11 and 12, two types of X-ray detectors 140 and 140 in which two types of X-ray detection sensors 14 a and 14 b similar to the above are formed for each of the two X-ray detection sensor substrates 14 and 14. These X-ray detectors 140 and 140 are detachably attached to a sensor holding unit 10a formed in the X-ray detection unit 10. Further, a secondary slit plate 16 in which two types of secondary slits 16a and 16b similar to the above are formed is supported in front of the sensor holding portion 10a through a slide mechanism 16e so as to be laterally movable. Reference numeral 16f denotes a motor for moving the secondary slit plate 16 laterally. The rotational power of the motor 16f rotates the rotary disc 16g to move the secondary slit plate 16 laterally.

  When any X-ray detector 140 is mounted on the sensor holding unit 10a, the identifier 14d or 14e attached to each X-ray detection sensor substrate 14 is detected, and the secondary slit plate 16 is based on this detection information. Is moved laterally by the drive of the motor 16f, and the secondary slits 16a and 16b corresponding to the X-ray detection sensors 14a and 14b are set. Since the subsequent execution of each X-ray imaging mode is the same as described above, the description thereof is omitted here. The X-ray detector 140 provided with the vertically long X-ray detection sensor 14b can also be used for cephalometric imaging as in the second embodiment if the X-ray detection sensor 14b is about 225 × 6 mm. It is the same.

  FIG. 13 shows an X-ray detector 140 having two types of X-ray detection sensors 14a and 14b similar to those described above, and two types of X-ray detection sensors 14a and 14b by adjusting the X-ray generator 9 side. Can be selectively used, that is, the panoramic imaging mode and the CT imaging mode can be selectively executed. In the example of FIG. 13A, the solid line position is the execution position of the panoramic imaging mode, and the alternate long and short dash line position is the execution position of the CT imaging mode. At the execution position of the panoramic imaging mode, the X-ray beam XB is directed to the X-ray detection sensor 14b. By slightly shifting the primary slit plate 12 from this state, the X-ray beam XB is changed as shown by a one-dot chain line. It can be directed to the X-ray detection sensor 14a. After adjusting with the XY table 8 so that the turning center of the turning arm 6 comes to the center position of the tooth of interest t, the CT imaging mode is executed by turning the turning arm 6. In this case, for example, by driving the motor 9e shown in FIG. 7, the X-ray generator 9 can be swung, and the directivity direction of the X-ray beam XB can be changed in the same manner.

  In the example of FIG. 13B, the X-ray generator 9 is slidable with respect to the swivel arm 6, and the X-ray generator 9 is displaced together with the primary slit plate 2 from the solid line position in the figure to the one-dot chain line position. By switching the directivity direction of the X-ray beam XB from the X-ray detection sensor 14b to the X-ray detection sensor 14a, switching from the panoramic imaging mode to the CT imaging mode is enabled. In both of these examples, it goes without saying that switching from the CT imaging mode to the panoramic imaging mode is also possible. Moreover, although omitted in the drawing, it goes without saying that secondary slits corresponding to the X-ray detection sensors 14a and 14b should be provided respectively. The switching setting of each X-ray imaging mode in a state where the X-ray detector 140 is fixed is also employed in the same manner as described above, and these are arbitrarily selected and adopted as a design matter.

  In each of the above-described embodiments, a dental X-ray imaging apparatus has been described as an example. However, the present invention is not limited to this and can be applied to otolaryngology, surgery / internal medicine, and other medical uses. In addition, although the swivel arm 6 swivels horizontally, it can also be used for tomography of the patient's torso by swiveling vertically around the horizontal axis. Further, although the X-ray detection sensor 14a has a substantially square rectangular shape, other rectangular shapes or circular shapes can be adopted as long as the planar shape has a two-dimensional extension. In particular, since the MOS is expensive, it is desirable from the viewpoint of economy to make the shape as small as possible when cutting from the wafer.

It is a front view of the dental X-ray imaging apparatus as an example of the medical X-ray imaging apparatus of the present invention. It is the left side view. It is a whole block diagram of the same apparatus. It is the same control block diagram. It is a drive circuit diagram of the X-ray detection sensor by MOS. It is a flowchart of imaging mode using the X-ray imaging apparatus. It is a figure explaining the detail of X generator, (a) is a longitudinal cross-sectional view, (b) is a perspective view of the principal part. It is a longitudinal cross-sectional view which shows an example of an X-ray detection part. It is a disassembled perspective view of the principal part of the X-ray detection part. It is a longitudinal cross-sectional view which shows another example of an X-ray detection part. It is a longitudinal cross-sectional view which shows another example of an X-ray detection part. It is a disassembled perspective view of the principal part of the X-ray detection part. (A) (b) is explanatory drawing which shows the aspect of the positional relationship of an X-ray generator and an X detection part at the time of fixing an X-ray detector.

Explanation of symbols

3b Body frame (support)
5d Cefaro X-ray detector 9 X-ray generator 10 X-ray detector 12a Primary slit 12b Primary slit 14 X-ray detection sensor substrate (substrate)
14a X-ray detection sensor (the other electrical imaging means)
14b X-ray detection sensor (one electrical imaging means)
16a Secondary slit 16b Secondary slit 29 Control means 30 Column base 30a Support shaft 140 X-ray detector A Dental X-ray imaging apparatus (medical X-ray imaging apparatus)
XB X-ray beam

Claims (17)

A support member for the swivel member, a swivel member that is turnably supported by the support member, an X-ray generator provided at one part of the swivel member, and an X-ray generator facing the other part of the swivel member A medical X-ray imaging apparatus comprising an X-ray detection unit provided;
The X-ray detection unit can be equipped with two types of electrical imaging means having different shapes, and one of the two types of electrical imaging means has an elongated shape, and the other has a planar shape extending in a two-dimensional direction. The medical X-ray imaging apparatus is characterized in that the two types of electrical imaging means are selectively used according to the X-ray imaging mode. The medical X-ray imaging apparatus according to claim 1,
A medical X-ray imaging apparatus, wherein the two types of electrical imaging means are formed on one side of a single substrate. The medical X-ray imaging apparatus according to claim 2,
A medical X-ray imaging apparatus characterized in that the one type of substrate can be displaced with respect to the X-ray detection unit, whereby the two types of electrical imaging means can be selectively used. The medical X-ray imaging apparatus according to claim 2,
Medical X-ray imaging characterized in that the two types of electrical imaging means can be selected and used by making the X-ray beam pointing direction relative to the X-ray detector of the X-ray generator variable. apparatus. The medical X-ray imaging apparatus according to claim 1,
Each of the two types of electrical imaging means is formed on both surfaces of a single substrate, and the two types of electrical imaging means can be selectively used by inverting the substrate. A medical X-ray imaging apparatus. The medical X-ray imaging apparatus according to claim 1,
The two types of electrical imaging means are formed on the peripheral surface of a columnar base that is rotatably attached to the X-ray detection unit, and the two types of electrical imaging means are rotated by rotating the columnar base around the axis. A medical X-ray imaging apparatus characterized in that an imaging means can be selected and used. The medical X-ray imaging apparatus according to claim 1,
The two types of electrical imaging means are respectively formed on two separate substrates, and both and / or one of the two substrates is detachably or detachably mounted on the X-ray detection unit. Accordingly, a medical X-ray imaging apparatus characterized in that the two types of electrical imaging means can be selectively used. The medical X-ray imaging apparatus according to any one of claims 1 to 7,
A medical X-ray imaging apparatus characterized in that said one electrical imaging means comprises a CCD and the other electrical imaging means comprises a MOS. The medical X-ray imaging apparatus according to any one of claims 1 to 7,
A medical X-ray imaging apparatus characterized in that both the one electrical imaging means and the other electrical imaging means are made of MOS. The medical X-ray imaging apparatus according to any one of claims 1 to 9,
The X-ray imaging mode is a panoramic imaging mode and a CT imaging mode, wherein the one electrical imaging unit corresponds to the panoramic imaging mode and the other electrical imaging unit corresponds to the CT imaging mode. Medical X-ray imaging device. The medical X-ray imaging apparatus according to claim 10,
The X-ray imaging mode further includes a cephalometric imaging mode, wherein at least one of the electrical imaging means is detachable from the X-ray detection unit, and the one electrical imaging means is an X-ray for the cephalometric imaging mode. A medical X-ray imaging apparatus characterized in that it can be attached to and detached from a detection unit, and is formed so that its shape can also be used in a cephalometric imaging mode. The medical X-ray imaging apparatus according to any one of claims 1 to 11,
A medical X-ray imaging apparatus comprising control means for selecting and setting an X-ray imaging mode based on selection information of the two types of electrical imaging means. The medical X-ray imaging apparatus according to claim 11,
The control means performs turning control of a turning member based on a turning pattern according to a selected and set X-ray imaging mode, X-ray generation control in an X-ray generator, and drive control of the selected electrical imaging means. A medical X-ray imaging apparatus. The medical X-ray imaging apparatus according to claim 13,
The control means controls to switch the primary slit on the X-ray generator side and / or the secondary slit on the X-ray detector side to a suitable one according to the selected X-ray imaging mode. A characteristic medical X-ray imaging apparatus. A support member for the swivel member, a swivel member that is turnably supported by the support member, an X-ray generator provided at one part of the swivel member, and an X-ray generator facing the other part of the swivel member An X-ray detector attached to the X-ray detection unit of a medical X-ray imaging apparatus including an X-ray detection unit provided;
It consists of a single substrate and two types of electrical imaging means formed on the plate surface of the substrate, one of the two types of electrical imaging means being elongated and the other spreading in the two-dimensional direction. An X-ray detector characterized by having a planar shape. The X-ray detector according to claim 15, wherein
An X-ray detector, wherein one of the two types of electrical imaging means is composed of a CCD, and the other electrical imaging means is composed of a MOS. The X-ray detector according to claim 15, wherein
An X-ray detector characterized in that both of the one electrical imaging means and the other electrical imaging means are made of MOS.

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