WO2015125589A1 - Appareil d'imagerie à rayons x - Google Patents

Appareil d'imagerie à rayons x Download PDF

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Publication number
WO2015125589A1
WO2015125589A1 PCT/JP2015/052745 JP2015052745W WO2015125589A1 WO 2015125589 A1 WO2015125589 A1 WO 2015125589A1 JP 2015052745 W JP2015052745 W JP 2015052745W WO 2015125589 A1 WO2015125589 A1 WO 2015125589A1
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Prior art keywords
ray
imaging apparatus
detector
arm
ray imaging
Prior art date
Application number
PCT/JP2015/052745
Other languages
English (en)
Japanese (ja)
Inventor
明敏 勝又
政廣 辻田
竜也 長野
昌也 北尾
浩一 尾川
Original Assignee
株式会社テレシステムズ
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from JP2014031911A external-priority patent/JP2015156886A/ja
Priority claimed from JP2014037037A external-priority patent/JP2015159973A/ja
Application filed by 株式会社テレシステムズ filed Critical 株式会社テレシステムズ
Publication of WO2015125589A1 publication Critical patent/WO2015125589A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/51—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for dentistry
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A61B6/035—Mechanical aspects of CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/10—Safety means specially adapted therefor
    • A61B6/107—Protection against radiation, e.g. shielding
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4405—Constructional features of apparatus for radiation diagnosis the apparatus being movable or portable, e.g. handheld or mounted on a trolley
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
    • A61B6/4452—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit and the detector unit being able to move relative to each other
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/44—Constructional features of apparatus for radiation diagnosis
    • A61B6/4429—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units
    • A61B6/447—Constructional features of apparatus for radiation diagnosis related to the mounting of source units and detector units the source unit or the detector unit being mounted to counterpoise or springs

Definitions

  • the present invention relates to an X-ray imaging apparatus using X-rays, and in particular, faces an X-ray tube and a detector that detects X-rays irradiated from the X-ray tube and transmitted through an imaging region of a subject. And an X-ray imaging apparatus having a structure for rotating the X-ray tube and the detector around a subject.
  • a panoramic imaging apparatus that obtains a panoramic image in which a curved dentition is developed in a two-dimensional plane has been put into practical use.
  • This panoramic imaging apparatus normally has a pair of an X-ray tube and a detector having vertically long two-dimensionally arranged pixels around the oral cavity of a subject along a dentition whose rotation center is assumed.
  • a mechanism for rotating the center of rotation in a complicated manner so as to draw a trajectory is provided.
  • a constant value is maintained between the X-ray tube and the detector.
  • the above-described constant trajectory is a trajectory for focusing on a reference tomographic plane (a tomographic plane existing three-dimensionally) set in advance along a dentition regarded as a standard shape and size.
  • a reference tomographic plane a tomographic plane existing three-dimensionally
  • X-rays emitted from the X-ray tube are transmitted through the subject at regular intervals, and detected as digital frame data by the detector.
  • frame data focused on the reference tomographic plane is collected at regular intervals. This frame data is reconstructed by the tomosynthesis method to obtain a panoramic image of the reference tomographic plane.
  • Patent Document 6 discloses an example of a panoramic imaging apparatus having an imaging system in which an X-ray tube and a detector can both rotate independently of each other so as to form a circular orbit around the same center point. .
  • the jaw is positioned in the circular orbit.
  • the velocity pattern of the X-ray tube and the detector is controlled so that the X-ray irradiated from the X-ray tube always faces the detection surface of the detector.
  • JP-A-57-203430 JP-A-6-88790 JP-A-10-295680 US Patent Publication US2006 / 0203959 A1 JP2007-136163A International Publication WO2012 / 008492
  • the present invention has been made in view of the above circumstances, and provides an X-ray imaging apparatus with low X-ray exposure that can increase the degree of freedom in setting a focal plane in an imaging space, that is, setting an X-ray path trajectory. Its main purpose is to do.
  • X-ray imaging with low X-ray exposure with the ability to increase the degree of freedom of setting a partial focal plane and X-ray path in the imaging space, and accurately teaching the desired precision imaging range
  • Another object is to provide a device.
  • another object is to provide an X-ray imaging apparatus with low X-ray exposure that is easy to convey and easy to position, and can increase the degree of freedom in setting a focal plane in the imaging space.
  • an X-ray imaging apparatus has an X-ray tube having a point-like focal point and irradiating X-rays having a spread from the focal point, A detector that detects the X-rays emitted from the X-ray tube and outputs data corresponding to the amount of the X-rays, and passes the X-ray tube and the detector through a predetermined center of rotation. It is configured to be rotatable around a central axis.
  • the apparatus is configured such that the X-ray tube receives the X-ray so that the X-ray tube is accommodated, and the tube accommodating portion is rotatable around a first axis parallel to the central axis.
  • An X-ray tube arm having a tube support portion to support, a first driving means for rotating the tube housing portion around the first axis with respect to the tube support portion, and the X-ray incident thereon
  • a detector including a detector accommodating portion that accommodates the detector and a detector supporting portion that rotatably supports the detector accommodating portion around a second axis parallel to the central axis.
  • Third driving means that supports the same axis so as to be drivable and drives both arms to rotate around the central axis. The first and second in accordance with a speed pattern in which the X-ray tube arm, the detector arm, the tube housing portion, and the detector housing portion are rotated independently of each other for scanning by the X-ray.
  • control means for controlling the third drive means.
  • the first distance from the central axis to the first axis is set to a value larger than the second distance from the central axis to the second axis, and the X-ray tube And the detector can be rotated along different circular orbits.
  • the X-ray tube and the detector are rotated independently of each other around the same central axis passing through one rotation center.
  • the X-ray tube and the detector can be rotated around first and second axes parallel to the rotational axis at their respective rotational positions. That is, since both the X-ray tube and the detector can rotate (attitude control), the two can always be kept facing each other.
  • the configuration is relatively simple and can be miniaturized.
  • the X-ray path can be easily changed, so that the imaging space can be drawn from various angles. For this reason, various focal planes can be set in the imaging space.
  • the imaging is performed by irradiating the imaging part of the subject located in the imaging space between the tube housing part and the detector housing part with a laser beam simulating the actual irradiation of the X-ray.
  • Teaching means capable of instructing a partial imaging range of a part before imaging; setting means for decoding the partial imaging range instructed by the teaching means and setting the speed pattern according to the decoding result; , Is provided.
  • an X having a function of increasing the degree of freedom in setting a partial focal plane in an imaging space and setting an X-ray path and teaching a desired precision imaging range accurately.
  • a line imaging apparatus can be provided.
  • the imaging space that holds the X-ray tube arm and the detector arm rotatably and allows the X-ray tube arm and the detector arm to rotate around the specific part.
  • the X-ray imaging apparatus moves to the back of the dental treatment chair, is positioned on the rear side of the dental treatment chair, and lies on the back of the dental treatment chair.
  • An apparatus for performing X-ray imaging by positioning a head in an imaging space between the X-ray tube and the detector, an operation unit operated by an operator, and transmission for transmitting an operation given to the operation unit Means, a position specifying means for specifying a predetermined position when the X-ray imaging apparatus is laid on the chair, and the X-ray imaging by being locked to the position specifying means according to the operation transmitted by the transmitting means.
  • Fixing means for fixing the device in the predetermined position.
  • FIG. 1 is a perspective view showing a front side of an X-ray panoramic imaging apparatus as an X-ray imaging apparatus according to the first embodiment of the present invention.
  • FIG. 2 is a perspective view showing the back of the X-ray panoramic imaging apparatus as the X-ray imaging apparatus according to the first embodiment.
  • FIG. 3 is a perspective view for explaining the positional relationship between the X-ray panoramic imaging apparatus and the dental treatment chair and the position of the subject at the time of imaging.
  • FIG. 4 is a partial cross-sectional view illustrating a scattered radiation shielding plate built in the bottom surface.
  • FIG. 5 is a perspective view for explaining the scattered radiation shielding cover.
  • FIG. 6 is a diagram illustrating a four-surface shielding structure including a scattered radiation shielding cover that covers the upper surface and both side surfaces and a scattered radiation shielding plate that covers the bottom surface portion.
  • FIG. 7 is a side view for explaining the 4-axis independent drive of the X-ray panoramic imaging apparatus.
  • FIG. 8 is a front view for explaining the 4-axis independent drive of the X-ray panoramic imaging apparatus.
  • FIG. 9 is a block diagram showing a part of the electrical configuration of the X-ray panoramic imaging apparatus.
  • FIG. 10 is a diagram illustrating the relationship between a standard dentition, a 3D reference tomographic plane, and an X-ray path.
  • FIG. 10 is a diagram illustrating the relationship between a standard dentition, a 3D reference tomographic plane, and an X-ray path.
  • FIG. 11 is a graph illustrating a speed pattern instructing partial revolutions of the X-ray tube and the detector related to two axes in the four-axis independent control.
  • FIG. 12 is a graph illustrating a speed pattern instructing partial revolutions of the X-ray tube and the detector relating to the remaining two axes of the four-axis independent control.
  • FIG. 13 is a flowchart illustrating a procedure for panoramic shooting.
  • FIG. 14 is a diagram for explaining a typical rotational position of the X-ray tube and the detector during panoramic imaging and a state of positioning by a laser beam.
  • FIG. 15 is a perspective view of the internal structure of the apparatus main body mounted on the X-ray panoramic imaging apparatus according to the first modification as seen from the front.
  • FIG. 15 is a perspective view of the internal structure of the apparatus main body according to the first modification when viewed from the rear.
  • FIG. 17 is a perspective view illustrating a scattered radiation shielding cover according to the second modification. It is a figure explaining the conventional dental X-ray used in order to explain the X-ray panoramic imaging device concerning the 2nd embodiment of the present invention.
  • FIG. 19 is a diagram for explaining teaching employed in the second embodiment.
  • FIG. 20 is a diagram illustrating a configuration corresponding to the teaching device according to the second embodiment.
  • FIG. 21 is a diagram for explaining teaching.
  • FIG. 22 is a diagram for explaining teaching processing.
  • FIG. 23 is a diagram for explaining calculation of control data in teaching.
  • FIG. 24 is a flowchart for explaining the procedure of the partial shooting operation.
  • FIG. 24 is a flowchart for explaining the procedure of the partial shooting operation.
  • FIG. 25 is a graph illustrating a speed pattern of a target tooth related to partial imaging when it is assumed that there is a dentition along a standard trajectory.
  • FIG. 26 is a side view for explaining the position of the scattered radiation shielding plate provided on the back surface of the X-ray panoramic imaging apparatus according to the third embodiment of the present invention.
  • FIG. 27 is a diagram for explaining the attachment of an X-ray protective curtain that can be used in the third embodiment and that is detachably disposed on the front side during imaging.
  • FIG. 28 is a diagram illustrating a six-side shielding structure when the scattered radiation shielding means shown in both FIG. 26 and FIG. 27 is employed.
  • FIG. 29 is a side view showing an X-ray panoramic imaging apparatus and a floor fixing unit according to the fourth embodiment of the present invention.
  • FIG. 30 is a perspective view showing an X-ray panoramic imaging apparatus and a floor fixing unit according to the fourth embodiment.
  • FIG. 31 is a front view and a side view of the operation lever.
  • FIG. 32 is a schematic view taken along the line IX-IX in FIG. 32 for explaining the outline and operation of the link mechanism from the operation lever to the positioning pin together with the positioning operation of the positioning pin.
  • FIG. 33 is a diagram for explaining an outline of a cross-sectional structure taken along lines II and II-II in FIG.
  • FIG. 34 is a diagram for explaining the structure of the positioning pin and the vertical movement operation.
  • FIG. 35 is a perspective view of the floor fixing portion.
  • FIG. 36 is a cross-sectional view along a direction orthogonal to the longitudinal direction of the floor fixing portion.
  • FIG. 37 is a block diagram showing the connection of sensors, LEDs, and processors for detecting the vertical movement of the positioning pins.
  • FIG. 38 is a diagram for explaining a modification of the position detection means of the floor fixing portion for positioning.
  • FIG. 39 is a diagram for explaining another modified example of the position detecting means of the floor fixing portion for positioning.
  • the panoramic imaging apparatus 1 is configured as a dental diagnostic apparatus that captures a panoramic image of a subject's jaw (including a dentition).
  • the panoramic imaging apparatus 1 teaches the apparatus 1 itself the angle and range of X-ray irradiation for performing the precision imaging, and reflects the taught angle and range.
  • the teaching device for setting the control data is functionally integrated.
  • this panoramic imaging apparatus a pseudo three-dimensional tomographic image of the subject's jaw (the image itself is a two-dimensional image, but three-dimensionally according to the shape of an imaging region such as a dentition).
  • the displayed cross-sectional image) can be taken.
  • region of the dentition of a jaw part more precisely can also be performed.
  • the control of the rotational operation for precision photographing is based on an original control method called “4-axis independent control”.
  • the “4-axis independent control” employs a unique anti-scattering structure because the apparatus is portable and can be used on the side of the dental treatment chair 2. For this reason, first, the configuration of the entire apparatus including the scattered radiation prevention structure will be described, followed by the description of the configuration of the 4-axis independent control, and then the configuration of the teaching device for precision imaging.
  • the X-ray imaging apparatus is configured as a panoramic imaging apparatus, but the X-ray imaging apparatus is not necessarily limited to the dental field.
  • This X-ray imaging apparatus may be configured to image various other parts such as otolaryngology imaging and bone / joint parts of limbs.
  • this X-ray imaging apparatus may be implemented as an X-ray CT apparatus.
  • FIG. 1 and FIG. 2 show the appearance of the dental X-ray panoramic imaging apparatus 1 according to this embodiment from the front side and from the back side.
  • FIG. 3 shows a state in which the panoramic photographing apparatus 1 is used while being positioned on the side of the dental treatment chair 2.
  • the panoramic photographing apparatus 1 includes a pedestal portion 12 on which four casters 11 (moving means) are mounted, a power supply box 13 mounted on the pedestal portion 12, and a pedestal portion 12. And a console 15 equipped with a computer for controlling and image processing.
  • the console 15 is connected to the main body BD of the apparatus 1 via a cable or via wireless communication.
  • the main body BD means an apparatus portion excluding the console 15 and a floor fixing portion 53 (see FIG. 3) described later.
  • the casters 11 are provided at the four corners of the lower surface of the base 12. For this reason, the dentist or the operator can move by pushing the panoramic imaging apparatus 1 and can freely move from room to room or between the room place and the side of the dental treatment chair 2. .
  • the caster 11 can be locked and unlocked by depressing or raising a pedal 11P (see FIG. 2).
  • the elevator 14 includes an elevating mechanism (not shown) in its interior, and is electrically driven with respect to the pedestal portion 12 (that is, the floor surface, that is, the dental treatment chair 2) in an arbitrary range of height (eg, 10 to 15 cm). It is configured to be movable up and down at a height position.
  • the power supply box 13 includes a power supply circuit that supplies necessary power to each part of the system.
  • the elevator 14 provides an imaging space S having a substantially rectangular parallelepiped shape for performing X-ray scanning with the head H of the patient P positioned as shown in FIG.
  • XYZ orthogonal coordinates as shown in the figure can be set if the vertical movement direction of the elevator 14 is the Y axis. Since the head H of the patient P is positioned in the imaging space (object space) S as shown in FIG. 3 at the time of X-ray imaging, the direction of the Z axis is the direction from the top of the head H toward the toes (median) Line direction). For this reason, the direction of the Z axis coincides with the body axis direction. Furthermore, since the direction of the Z axis is also the front-rear direction of the device 1, it can also be called the front-rear direction. In the present embodiment, the side where the head H of the subject P is put into the imaging space S of the panoramic imaging apparatus 1 is referred to as the front surface (front surface), and the opposite surface is referred to as the rear surface (back surface).
  • the elevator 14 includes a bottom surface portion 14A located on the lower side thereof and a back surface portion 14B located on the bottom surface portion 14A in contact with the bottom surface portion 14A on the back surface side in the X-axis direction. Further, the elevator 14 further includes a scattered radiation shielding cover (part of the shielding body) which overlaps and overlaps both sides of the bottom surface portion 14A, that is, both sides in the X-axis direction and can be manually slid in the front-rear direction. ) 14C.
  • the scattered radiation shielding cover 14C is supported by rails RL provided on both lateral sides of the bottom surface portion 14A, and is slidably engaged in the front-rear direction. In order to perform this slide manually, a handle 16 is attached to the upper side and the rear side of the scattered radiation shielding cover 14C.
  • the scattered radiation shielding cover 14C serves as a first shielding body that shields scattered radiation of X-rays.
  • the bottom surface portion 14A is formed of a member formed by folding a rectangular resin or metal plate and joining both ends thereof to have a certain height and bend toward the outside in the height direction, that is, the Y-axis direction.
  • the inside of this bending member is hollow. The reason for this curvature is that the imaging space S is secured as wide as possible and the design is taken into consideration.
  • a scattered radiation shielding plate (second shielding member) 20 made of a lead plate is attached to the upper side of the cavity inside the bottom surface portion 14A.
  • a part of the edge in the horizontal direction (X-axis direction) of the scattered radiation shielding plate 20 is folded along the folding of the bottom surface portion 14A in the height direction (Y-axis direction).
  • the lead plate has a thickness of 0.3 mm and functions as a second shielding body that shields scattered X-ray rays.
  • a mechanism part including a drive system including a motor, a power transmission mechanism, and the like and an encoder (rotational position sensor) for monitoring the operation of the drive system is built in the back surface portion 14B of the elevator 14.
  • two arms 21 and 22 coupled to two electric motors that can rotate independently of each other project from the back surface portion 14B into the imaging space S.
  • These arms 21 and 22 have an L-shaped X-ray tube arm 21 with an X-ray tube 23 for irradiating fan-shaped X-rays at the tip side and a detector 24 for detecting X-rays at the tip side.
  • L-shaped detector arm 22 is an L-shaped X-ray tube arm 21 with an X-ray tube 23 for irradiating fan-shaped X-rays at the tip side and a detector 24 for detecting X-rays at the tip side.
  • the other ends of the arms 21 and 22 are coaxially linked around the rotation center O and can rotate independently of each other (see arrows T and D in FIG. 1).
  • the motor is, for example, a stepping motor, and its rotational position is detected by an encoder (not shown).
  • a virtual straight line passing through the rotation center O and parallel to the Z axis is referred to as a central axis CA.
  • the central axis CA is an axis that can also be called the rotation center axis of the arm, and is physically different from the rotation center O of the arm, but is present at the same position when observing along the Z-axis direction. .
  • each of the X-ray tube arm 21 and the detector arm 22 supports only the tip side portion, that is, the portion containing the X-ray tube 23 and the detector 24 on the support side, that is, the back surface portion 14B.
  • the support portion can be independently rotated within a predetermined angle range with respect to the support portion side. Arrows T1 and D1 in FIG. 1 indicate this rotation. That is, the X-ray tube 23 and the detector 24 have a total of four degrees of freedom of independent rotation with respect to the back surface portion 14B.
  • the X-ray tube 23 incorporates a collimator (not shown). This collimator collimates the X-rays irradiated by the X-ray tube 23 according to the shape of the X-ray incident window WD of the detector 24.
  • the X-ray incident window WD has an elongated two-dimensional opening. For this reason, the X-rays irradiated from the X-ray tube 23 are narrowed down to a fan beam XB having a rectangular cross section in accordance with the size of the X-ray incident window WD.
  • the detector 24 has a structure in which a plurality of modules in which semiconductor elements that directly convert X-rays into electrical signals are arranged in two-dimensional pixels are arranged in a plurality of columns.
  • the head H of the subject P is located in the imaging space S as will be described later.
  • the X-ray tube 23 and the detector 24 are positioned substantially opposite to each other across the jaw.
  • the X-ray tube 23 and the detector 24 rotate independently of each other over the head H over an angle range of, for example, 220 ° (see the arrow in FIG. 3).
  • X-rays are emitted from the tube 23 continuously or in pulses.
  • the X-ray XB irradiated from the X-ray tube 23 passes through the jaw of the head H and is detected by the detector 24.
  • the electric signal output from the detector 24 is sent as frame data to the image processor of the console 15 at a constant rate.
  • the image processor performs a shift-and-add process based on the tomosynthesis method on the frame data, and reconstructs a panoramic image along a cross section in which, for example, the dentition of the jaw is curved along the dentition surface.
  • one rotation center O is set when viewed from the Z-axis direction.
  • an L-shaped teaching arm 25 is provided coaxially with the rotation shaft on the apparatus main body side of the arms 21 and 22.
  • the teaching arm 25 is used for designating a range of a part (target tooth) of a dentition that the dentist wants to examine particularly precisely. In other words, it has a position designation function that is performed in so-called partial photographing or precision photographing, which is performed in the photographing by the conventional intraoral photographing method.
  • a laser beam can be irradiated from the tip of the teaching arm 25.
  • the dentist visually confirms the position where the laser beam hits the dentition while holding the tip of the teaching arm 25 and manually rotating the arm around the jaw.
  • the teaching arm 25 is provided with an encoder and a switch (not shown). For this reason, when the angle position and the angle of the transmitted X-ray are determined, the dentist can store the setting information by pressing the switch. This stored information is used by the control unit of the console 15 at the time of actual imaging, and the X-ray irradiation operation and the rotation operation of the X-ray tube 23 and the detector 24 are controlled according to the information.
  • the scattered radiation shielding cover 14C is responsible for defining the upper surface and the left and right side surfaces of the imaging space S and shielding X-rays as shown in FIG.
  • the scattered radiation shielding cover 14 ⁇ / b> C has a shape obtained by bending a plate having an X-ray shielding function with a constant width into a generally inverted U shape.
  • the scattered radiation shielding cover 14C has a flat upper surface portion (ceiling body) 14U and both side surface portions (wall bodies) 14L and 14R that are curved and integrally formed from the upper surface portion 14U.
  • the scattered radiation shielding cover 14C has an X-ray shielding function as a whole, the scattered radiation shielding cover 14C is formed by combining two kinds of members relating to light transmittance. Specifically, the scattered radiation shielding cover 14C includes a translucent portion 14TR having translucency and a non-translucent portion having non-translucency integrally coupled to the translucent portion 14TR. 14NT. Both the translucent portion 14TR and the non-translucent portion 14NT partially cover the upper surface portion 14U and the side surface portions 14L and 14R.
  • the non-translucent portion 14NT is formed in an inverted L shape when viewed from the side so as to cover a part of the rear surface side and extend to the bottom surface side across the upper surface portion 14U and both side surface portions 14L, 14R. ing.
  • This non-translucent portion 14NT is formed as a laminated body in which, for example, a lead plate having a thickness of 0.3 mm is sandwiched between resin or metal plates.
  • the translucent portion 14TR is generally formed in an inverted U shape so as to cover the front side of the non-translucent portion 14NT across the upper surface portion 14U and the side surface portions 14L, 14R.
  • the height of the left and right sides of the light-transmitting portion 14TR is shorter than that of the non-light-transmitting portion 14NT, the bottom end of the light-transmitting portion 14TR is supported by the non-light-transmitting portion 14NT. It is like that.
  • the translucent portion 14TR is formed of a transparent acrylic resin having a thickness of 8.5 mm containing a lead component, and thereby has an X-ray shielding ability of a lead equivalent of 0.3 mmPb. Therefore, the translucent portion 14TR has an X-ray shielding function, but also has light transparency.
  • the acrylic resin itself is transparent, it contains a lead component, so it actually has a yellowish color but is translucent. For this reason, as will be described later, when the head H of the patient P enters the imaging space S, the patient can see the outside of the cover. Of course, the operator can also visually observe the inside of the imaging space S.
  • an X-ray shielding device is configured by the scattered radiation shielding cover 14C and the scattered radiation shielding plate 20 on the bottom surface portion 14C.
  • the entire portion has the function of shielding the scattered radiation, while the part of the scattered radiation shielding portion 14TR has light transmittance.
  • the X-ray shielding function is given to the top surface, both side surfaces, and the bottom surface that define the imaging space S.
  • a cover portion 51 containing a fixing pin 50 is provided at the front end of the pedestal portion 12.
  • the pin 50 moves up and down in conjunction with an operation lever 52 (see FIG. 2) provided on the upper edge of the back surface part 14 via a wire mechanism (not shown).
  • a floor fixing portion 53 having a substantially triangular shape in a side view and having a hole into which the pin 50 can be inserted is fixed at a predetermined position on the rear surface of the dental treatment chair 2. .
  • the pin 50 can be pushed down by moving the apparatus main body BD and operating the operation lever 52 in a state where the tip end position thereof is aligned with the floor fixing portion 53.
  • the apparatus main body BD is positioned with respect to the dental treatment chair 2 (see FIG. 3).
  • the pin 50 is pulled up and released from the floor fixing portion 53 by operating the operation lever 52. Thereby, apparatus main body BD can be moved to another place.
  • a moving handle 54 is fixedly provided on both sides of the operation lever 52 at the upper end of the back surface portion 14B. Therefore, the operator can easily move the apparatus main body BD along with the free rotation of the caster 11 by holding the moving handle 54.
  • the position and shape of the moving handle 54 are not limited to the position and structure tightened in FIG. 2, and if the operator can manually push or move the apparatus main body BD, the number and the shape are included. Can be freely deformed.
  • the moving handle 54 may be formed as an L-shaped handle that is fixed to both corners of the upper end portion of the back surface portion 14B and has a horizontal portion and a vertical portion integrally.
  • the back surface portion 14B is provided with an irradiation switch 56 for commanding X-ray irradiation and rotation of the X-ray tube / detector via a cord 55 having a length of 2 m, for example.
  • This irradiation switch 56 is configured as a deadman switch. That is, X-ray irradiation is performed only while the push button of the irradiation switch 56 is being pressed. The switch signal of the irradiation switch 56 is sent to the console 15.
  • a portable panoramic photographing apparatus 1 having a height of about 100 to 115 cm, a width of about 80 to 95 cm, and a depth of about 75 to 90 cm is provided.
  • the imaging space S is regarded as a substantial X-ray shielding room. You can also Therefore, in this embodiment, the X-ray shielding chamber (that is, the device 1) can be easily carried to an arbitrary place by the caster 11 by grasping and pushing the moving handle 54 and can be used there. .
  • the panoramic imaging apparatus 1 includes the X-ray tube arm 21 and the detector arm 22 that extend in the lateral direction from the elevator section of the elevator 14.
  • the two arms 21 and 22 are both formed in an approximately L shape, and the ends of the support portions (tube support portions and detector support portions) 21L and 22L of the arms 21 and 22 respectively.
  • the parts are superposed so as to overlap each other and are attached to the elevator 14.
  • the elevator 14 is equipped with a rotary drive mechanism 83 that can rotate the two arms 21 and 22 independently of each other, that is, at different speeds.
  • the above-described X-ray tube 23 and detector 24 are mounted on the opposing arm portions 21A and 22A on the distal ends of the two arms 21 and 22, respectively.
  • a slit (diaphragm) 84 for forming X-rays into a fan shape is disposed on the front surface of the X-ray tube 23 on the X-ray irradiation side.
  • the opening area of the slit 84 is variable, and the size of the opening area is controlled by an opening driving unit 85 such as a motor described later.
  • the rotation drive mechanism 83 and the arms 21 and 22 constitute support means for supporting the X-ray tube 23 and the detector 24 so that they can be driven independently of each other.
  • the X-ray tube 23 is configured as a rotary anode type X-ray tube used for an appropriate anode material such as tungsten.
  • the X-ray tube 23 has a point-like tube focus (X-ray focus) (for example, a diameter of 0.1 mm to 0.5 mm: 0.15 mm in this embodiment) FP.
  • the X-ray tube 23 irradiates X-rays in response to driving power supplied from a high voltage generator described later.
  • the X-rays irradiated from the X-ray tube 23 are narrowed by the slit 84 and formed into a fan-shaped X-ray beam.
  • the X-ray beam then passes through the jaw JW of the subject P and attenuates, and transmitted X-rays reflecting the attenuated state enter the detector 24.
  • the jaw JW of the subject P is positioned at a predetermined position in the three-dimensional imaging space S defined between the X-ray tube 23 and the detector 24. For this reason, the X-ray tube 23 and the detector 24 face each other (face to face) with the jaw portion interposed therebetween.
  • the irradiated X-ray beam passes through the slit 84 and then passes through the jaw portion JW (dentition etc.) and is detected by the detector 24.
  • the two arms 21 and 22 are independently rotated by the rotation driving mechanism 83.
  • the X-ray tube 23 and the detector 24 When viewed from the Z-axis direction, that is, the front-rear direction, the X-ray tube 23 and the detector 24 have a circular trajectory Tx centered on a central axis CA (rotation center O) determined in advance on the system side as shown in FIG. , Td, respectively.
  • the radii Dx and Dd from the central axis CA to the circular trajectories Tx and Td are set to different values in consideration of X-ray exposure, detection accuracy, downsizing of the apparatus, mechanical interference with the patient, and the like. Yes.
  • the reason why the distance (radius Dd) from the central axis CA to the detector 24 is smaller than that (radius Dx) from the central axis CA to the X-ray tube 23 is that the position of the detector 24 is as much as possible and the jaw JW This is to reduce the attenuation of the incident intensity of X-rays.
  • the distance (radius Dx) from the central axis CA to the X-ray tube 23 is set to a value that can ensure the distance between the X-ray tube and the skin defined by the standard.
  • the X-ray tube 23 and the detector 24 rotate around the jaw portion along predetermined circular trajectories Tx and Td around the central axis CA. During the rotation, irradiation and detection of the X-ray beam are executed at predetermined intervals.
  • the X-ray tube 23 and the detector 24 are always opposed to each other (facing each other), and X-ray irradiation and detection along a plurality of predetermined desired X-ray paths with respect to the jaw JW (dentition) are performed.
  • the X-ray tube 23 and the detector 24 are driven independently of each other at different angular velocities.
  • the facing arm portion housing the X-ray tube 23 and the detector 24.
  • the container housing portions 21A and 22A are independent from each other about the first axis (that is, the X-ray tube swing rotation central axis) AXs and the second axis (that is, the detector swing rotation central axis) AXd.
  • rotation spininning, that is, posture
  • rotational drive mechanisms 21B and 22B such as motors are provided on the arms 21 and 22, respectively (see FIG. 7).
  • the drive control of the rotation drive mechanisms 21B and 22B is executed by a controller provided in the power supply box 13 in accordance with a command from the console 15 described later.
  • the circular trajectories Tx and Td shown in FIG. 8 indicate the trajectories of the first and second axes AXs and AXd described above when viewed on the XY plane, respectively.
  • biaxial rotational degrees of freedom are given to the arms 2 and 22 that are driven to rotate independently of each other by the rotary drive mechanism 83 described above, so that the X-ray tube 23 rotates (so-called swinging rotation) and is detected.
  • Two-axis rotational freedom is given to the rotation (so-called swinging rotation) of the device 24. This gives a total of four axes of rotational freedom.
  • the detector 24 has a plurality of detection modules in which X-ray imaging elements are two-dimensionally arranged.
  • the plurality of detection modules are formed as blocks independent from each other, and are mounted on the substrate in a predetermined rectangular shape to form the entire detector 24.
  • the structure of the detector 24 and the processing of the detection signal by the sub-pixel method are known from, for example, International Publication WO 2012 / 0886648A1.
  • Each detection module is made of a semiconductor material that converts X-rays directly into electrical pulse signals. For this reason, the detector 24 is a photon counting X-ray detector of a direct conversion method using a semiconductor.
  • each detection module is 40 ⁇ 40 pixels, for example, the size of each pixel S n is 200 [mu] m ⁇ 200 [mu] m, for example.
  • This pixel size is set to a value that allows detection of incident X-rays as a collection of many photons.
  • Each pixel responds to the incidence of each photon of the X-ray and outputs an electric pulse having an amplitude corresponding to the energy of each photon. That is, each pixel can directly convert X-rays incident on the pixel into an electrical signal.
  • the detector 24 counts the incident X-ray photons for each pixel constituting the detection surface of the detector 24, and outputs the electric quantity data reflecting the counted value, for example, a high frame of 300 fps. Output at the rate. This data is also called frame data.
  • the semiconductor material of the semiconductor layer that is, the semiconductor cell
  • cadmium telluride semiconductor CdTe semiconductor
  • cadmium zinc telluride semiconductor CdZnTe semiconductor
  • silicon semiconductor Si semiconductor
  • thallium bromide T1Br
  • Mercury iodide HgI 2
  • a detector having a combination structure of a photodiode and a scintillator may be used instead of the detector using the semiconductor cell.
  • the four laser beams are used as positioning means. Specifically, a midline laser 211 provided on the upper side of the imaging space S side of the back surface portion 14B, a horizontal laser 212 provided at each predetermined position on the side surface of the opposing arm portion 22B of the detector arm 22, and an occlusal plane laser 213 and the canine laser 214 (see FIG. 7). These lasers 211 to 214 project a linear laser marker onto the head of the subject P during positioning, and their drive is controlled via the console 15.
  • the median laser 211 aligns the midline of the head H of the subject P
  • the horizontal laser 212 aligns the Frankfurt plane
  • the occlusal plane laser 213 aligns the occlusal plane
  • the canine laser 214 aligns the canines in the dentition. (See FIG. 14, (B ′)).
  • shock sensors 215 and 216 for detecting an impact are installed on the opposing arm portions 21B and 22B of the X-ray tube arm 21 and the detector arm 22 as fail-safe sensors, respectively (see FIG. 7). This is because, for example, when something hits the arms 21 and 22, it senses that and stops scanning, and the output signals of the shock sensors 215 and 216 are also sent to the console 15.
  • the console 15 includes an interface (I / F) 131 that performs input and output of signals, a controller 133 that is communicably connected to the interface 131 via a bus 132, and a first storage unit 134, a data processor (CPU) 135, a display device 136, an input device 137, a calibration calculator 138, a second storage unit 139, first to fourth ROMs 140A to 140D, and a threshold value assigner 140E.
  • I / F interface
  • the controller 133 controls the driving of the panorama photographing apparatus 1 in accordance with a program given in advance to the first ROM 140A. For this control, a command value is sent to the high voltage generator 140F that supplies a high voltage to the X-ray tube 23, a command value is sent to the opening drive unit 85 to change the opening area of the slit 84, and calibration is performed. A drive command to the operation calculator 138 is also included.
  • the first storage unit 134 stores frame data and image data that are count values sent from the detector 24 via the interface 131. Further, the controller 133 receives the switch signal of the irradiation switch 56 via the interface 131, and controls scanning as will be described later.
  • the controller 133 also receives the signals of the shock sensors 215 and 216 via the interface 131, and controls the continuation / stop of the scan described later. Further, the controller 133 is connected to the positioning lasers 151 to 154 via the interface 131, and is configured to drive the lasers 151 to 154 when a positioning command is issued.
  • the data processor 135 operates based on a program given in advance to the second ROM 140B under the control of the controller 133. Further, during panoramic shooting, the data processor 135, by its operation, adds to the frame data stored in the first storage unit 134 tomosynthesis based on a known calculation method called shift add add. Implement the law. Thereby, the panoramic image of the tomographic plane with the oral cavity of the subject P is obtained.
  • the display device 136 is responsible for displaying images to be created, information indicating the operation status of the apparatus, and operator operation information provided via the input device 137.
  • the input device 137 is used by an operator to give information necessary for imaging to the apparatus.
  • the calibration calculator 138 operates under the control of the controller 133 under a program built in the third ROM 140C in advance, and is given to each energy discrimination circuit for each pixel in the data counting circuit. Calibrate digital quantity thresholds for energy discrimination.
  • the threshold value assigner 140E calls the digital amount threshold value stored in the second storage unit 139 for each pixel and for each discrimination circuit at the time of imaging, and uses the threshold value as a command value as an interface.
  • the signal is transmitted to the photon counting circuit of the detector 24 via 131.
  • the threshold value assigner 140E executes a program stored in advance in the fourth ROM 140D.
  • the controller 133, the data processor 135, the calibration calculator 138, and the threshold value assigner 140E all include a CPU (central processing unit) that operates according to a given program. These programs are stored in advance in the first to fourth ROMs 140A to 140D, respectively.
  • the structure of the imaging space S is analyzed using a phantom, and the collection channel of the detector 24 is calibrated. Is done. This calibration is executed at an appropriate timing such as before imaging or during maintenance inspection.
  • FIG. 10 shows a standard dentition TR, a trajectory SS (referred to as a standard trajectory) of projection of the horseshoe-shaped 3D reference tomographic plane of the dentition TR onto the XY plane, the position of the cervical vertebra CS, and the subject P
  • An X-ray beam path XB at each rotation angle ⁇ in the circumferential direction CR of the jaw JW is illustrated.
  • the path XB indicates a path connecting the X-ray focal point FP of the X-ray tube 23 and the center position C in the horizontal width direction (Y-axis direction) of the detection surface 24A (see FIG. 8) of the detector 24.
  • the tube focal point FP of the X-ray tube 23 is located on the line of the first axis (that is, the central axis of swinging of the X-ray tube) AXs, and the detection surface of the detector 24
  • the center position C in the lateral width direction of 24A is located on the line of the second axis (that is, the center axis of rotation rotation of the detector) AXd.
  • a speed pattern for performing two types of photographing methods can be set for the locus SS (standard orbit) of the 3D reference tomographic plane.
  • the standard imaging is an imaging method in which X-rays are irradiated so as to avoid the left and right jaw bones as much as possible with respect to the locus SS.
  • the orthogonal imaging is an imaging method in which X-rays are irradiated so that the path is always orthogonal to the locus SS.
  • trajectory SS standard trajectory
  • orthogonal shooting a plurality of types of velocity patterns for standard imaging and / or orthogonal imaging are preliminarily rotated in a partial range in the circumferential direction around the central axis CA of the X-ray tube 23 (here, partial revolution).
  • This speed pattern is obtained by taking the scan time (for example, 12 seconds) on the horizontal axis and the revolution or rotation angle on the vertical axis.
  • the revolution means that the X-ray tube 23 and the detector 24 rotate or rotate in the circumferential direction along each of the trajectories Tx and Td that are separated from the central axis CA by a predetermined distance.
  • “partial” refers to rotating a partial range in the entire circumferential direction, and refers to a partial angular range in the 360 rotation range.
  • FIGS. 11 and 12 illustrate a speed pattern indicating the revolution and rotation of the X-ray tube 23 and a speed pattern indicating the revolution and rotation of the detector 24 when performing standard imaging and orthogonal imaging.
  • the curves A and B in FIGS. 11 and 12 are for orthogonal imaging for adults of the X-ray tube 23 and the detector 24 in the range of about 220 ° when the circumferential angle ⁇ is set as shown in FIG.
  • the revolving and rotation speed patterns are shown respectively.
  • the rotation speed is increased in these portions so that the left and right jawbone portions are scanned as roughly as possible, and the speed is set so as to be dense in the dentition TR portion.
  • curves A ′ and B ′ in FIGS. 11 and 12 respectively show the revolution and rotation speed patterns of the X-ray tube 23 and the detector 24 for standard imaging for adults in the range of about 220 °.
  • curves A and B in FIG. 12 show partial rotations of the X-ray tube 23 and the detector 24, that is, so-called swing patterns within a certain angle. As this constant angle, about ⁇ 15 ° is set. This angle is set to 0 ° when the X-ray tube 23 and the detector 24 face each other. As shown in FIG. 11, the swinging of the X-ray tube 23 and the detector 24 itself is not constant, so the X-ray path XB does not always pass through the central axis CA. There are far more X-ray paths XB with the central axis CA removed. This is to increase the degree of freedom in designing the X-ray path XB as indicated by the arrow YJ in FIG.
  • the types of speed patterns prepared in this embodiment are ⁇ Speed pattern of standard shooting for adults (speed pattern group consisting of curves A ′ and B ′ in FIG. 11 and curves A ′ and B ′ in FIG. 12), -Speed pattern for orthogonal shooting for adults (speed pattern group consisting of curves A and B in FIG. 11 and curves A and B in FIG. 12), Speed pattern for standard shooting for children (speed pattern group consisting of time-reduced curves A ′ and B ′ in FIG. 11 and time-reduced curves A ′ and B ′ in FIG. 12), ⁇ Adult orthogonal shooting speed pattern (speed pattern group consisting of time-reduced curves A and B in FIG. 11 and time-reduced curves A and B in FIG. 12), It is.
  • the velocity patterns of the X-ray tube 23 and the detector 24 are not necessarily those for the standard 3D reference tomographic plane as described above.
  • This may be a velocity pattern for an arbitrarily shaped 3D reference tomographic plane.
  • the shape of the projection trajectory (standard trajectory) SS on the XY plane of the 3D reference tomographic plane shown in FIG. 10 described above may be a horseshoe shape in which the vicinity of the front teeth is narrower or wider.
  • the back teeth may form a narrower or wider horseshoe shape.
  • the velocity pattern related to such a deformed shape can be prepared in advance on the system side, or can be calculated and stored in a computer at a medical site or a research site.
  • the plurality of speed patterns set with such a high degree of freedom are stored as a table in the first storage unit 134 (storage means: see FIG. 9). For this reason, the controller 133 reads out a desired speed pattern from the first storage unit 134 to the work area through interactive exchange with the operator. When the scan is started, the controller 133 controls the rotation drive mechanisms 83, 21B, and 22B shown in FIG. 9 according to the read speed pattern. As a result, X-rays irradiated from the X-ray tube 23 and incident on the detector 24 through the jaw JW of the subject P are designated by desired standard imaging or orthogonal imaging for each rotation angle ⁇ in the circumferential direction. Pass the path XB. For this reason, the detector 24 always outputs the detected frame data while maintaining a posture facing the X-ray tube 23. This frame data is reconstructed into a panoramic image by the data processor 135.
  • the apparatus 1 When using the X-ray panoramic imaging apparatus 1, first, the apparatus 1 is positioned at a predetermined position on the back side of the dental treatment chair 2 and fixed to the floor surface. At this time, the operation lever 52 described above is operated to push the pin 50 down, and the pin 50 is engaged with the floor fixing portion 53. Thereby, positioning and fixation with respect to the dental treatment chair 2 of the main body BD of the X-ray panoramic imaging apparatus 1 are achieved. This facilitates the positioning of the scan of the X-ray panorama apparatus 1 with respect to the head H of the patient P when the backrest is tilted while sitting on the dental treatment chair 2.
  • the controller 133 of the console 15 is activated and interactively executes the following processing.
  • the controller 133 displays a login screen on the display 136, and thus performs login (FIG. 13, step S1).
  • the controller 133 causes the display 136 to display a panoramic shooting GUI (graphical user interface) (not shown).
  • the dentist inputs patient information (imaging date, patient ID, patient name, etc.) from the patient information input screen provided by this GUI (step S2).
  • a shooting type is selected on the GUI screen of the display 136 (step S3).
  • one of the four types of shooting which is set by default, is standard shooting for adults, orthogonal shooting for adults, standard shooting for children, and orthogonal shooting for children. Selected.
  • an imaging method having a customized size trajectory is set, it may be selected.
  • the controller 133 reads a speed pattern for executing the selected imaging method from the table in the first storage unit 134 to the work area. For example, when standard shooting for adults is selected, four types of pattern data of speed patterns A ′ and B ′ illustrated in FIGS. 11 and 12 are read out.
  • shooting conditions are set (step S4).
  • This setting is to set the tube voltage and tube current.
  • the controller 133 automatically sets the recommended shooting conditions. It is.
  • the controller 133 displays the screen so that the dentist positions the patient P, and waits during that time (step S5).
  • the dentist causes the patient P and his / her attendant to wear X-ray protective clothing, and causes the patient P to sit on the dental treatment chair 2.
  • the scattered radiation shielding cover 14 ⁇ / b> C is manually retracted to the rear side (see an imaginary line “retraction position” in FIG. 3).
  • the X-ray tube arm 21 and the detector arm 22 are positioned at the respective standby positions (see FIG. 14A).
  • the backrest is tilted and the head H is introduced into the imaging space S.
  • the main body BD of the panoramic photographing apparatus 1 and the dental treatment chair 2 are fixed to each other via the floor surface. Therefore, the headrest HR (see FIG. 3) of the dental treatment chair 2 is located at the approximate center of the imaging space S.
  • the head H of the patient P is also guided to a substantially intermediate portion between the X-ray tube arm 21 and the detector arm 22 waiting in the imaging space S.
  • the dentist presses the GUI laser irradiation button (not shown) of the display 136 and presses the positioning irradiation button.
  • the controller 133 rotates only the detector arm 22 and moves it to a positioning position, that is, a position directly beside the patient's head H (see FIG. 14B).
  • the controller 133 drives the midline laser 211, the horizontal laser 212, the occlusal plane laser 213, and the canine laser 214 (step S6). These four types of laser beams are projected onto the face of the patient P (see FIG. 14B ′).
  • the GUI of the display 136 instructs the dentist to position the face of the patient P (step S7).
  • the dentist adjusts the height of the elevator 14 via the controller 133 so that the linear beam BM1 from the canine laser 214 matches the canine of the patient P.
  • the position of the patient's face is finely adjusted while viewing the beams from the remaining lasers 211 to 213.
  • the position of the patient in the body axis direction is adjusted so that the linear beam BM2 from the occlusal plane laser 213 matches the occlusal plane of the patient P.
  • the midline sagittal plane of the head H is aligned with the linear beam BM3 from the midline laser 211.
  • the Frankfurt plane is aligned with the linear beam BM4 emitted from the horizontal laser 212.
  • the scattered radiation shielding cover 14C is moved to the imaging position in the forward direction (see the solid line “imaging position” in FIG. 3). As a result, as shown by the solid line in FIG. 3, the head H of the subject P is positioned in the defined imaging space S.
  • the front surface of the scattered radiation shielding cover 14C may be covered with an X-ray protective cloth containing lead after this positioning. This can be easily performed by detachably attaching a hinge or the like formed on the edge of the upper front surface of the cover 14C.
  • the setup button on the GUI is pressed (step S8).
  • the controller 133 rotates the X-ray tube arm 21 and the detector arm 22 to a predetermined setup position (see FIG. 14C).
  • the dentist finally confirms this setup condition.
  • the state inside the scattered radiation shielding cover 14C such as the state of the patient P and the arm position, can be confirmed by observing through the window portion by the translucent portion 14TR.
  • the dentist performs a scan.
  • This scan is executed when the dentist holds the irradiation switch 56 and presses and keeps pressing the switch 56 from a slightly distant place (step S9).
  • the X-ray tube arm 21 and the detector arm 22 revolve independently of each other along the velocity pattern according to the selected imaging type, and the opposing arm portions 21A, 22A, that is, X
  • the rotational movements of the tube 23 and the detector 24 are controlled independently of each other. That is, the collection of frame data is performed by the scan based on the 4-axis independent control described above.
  • Symbols Ks and Kd in FIG. 14D schematically show the trajectory of the movement of the X-ray tube 23 and the detector 24 due to the revolving motion of the X-ray tube arm 21 and the detector arm 22.
  • step S10 the determination in step S10 is NO and the scan is continued as it is. However, in the case of YES determination, each drive unit is immediately instructed to stop scanning (step S11). This monitoring is the same for the shock sensor (steps S12 and S11).
  • step S13 the dentist continues to press the irradiation switch 56 and the scanning is automatically ended (step S13). That is, the X-ray tube arm 21 and the detector arm 22 scan while moving within the scan range ⁇ (for example, about 220 °) commanded by the operation pattern, and automatically return to the initial retracted position when the scan is completed. (See FIG. 14D).
  • ⁇ for example, about 220 °
  • the scattered radiation shielding cover 14C is retracted rearward to release the patient (step S13).
  • the frame data collected by this scan is stored in the first storage unit 134.
  • the data processor 135 reconstructs a tomographic image of the dentition TR from this frame data using a predetermined profile curve (a curve defining the amount of overlap between the frame data) for the shift & add process. be able to.
  • a predetermined profile curve a curve defining the amount of overlap between the frame data
  • the technique described in US-2012-0230467 A1 can be adopted.
  • FIGS. 15 and 16 show an example of the internal structure of the main body BD that can be mounted on the panoramic photographing apparatus 1 in place of the drive mechanism described above, and shows a state in which a cover or the like covering the outside is removed. Yes.
  • the structure is extremely simplified, and a base part BS that is positioned on the dental treatment chair 2 via the floor surface, and a tower part TW that can be height-adjusted from the base part BS,
  • the driving unit DV provided on the upper portion of the tower unit TW, and the arm unit AM which is attached to the tower unit TW at the upper position and is linked to the driving unit DV.
  • the base portion BS has the pedestal portion 12 as in the above-described embodiment, and a telescopic elevator 141 is mounted thereon.
  • the elevator 141 has the function of the elevator 14 described in the above-described embodiment.
  • the elevator 141 is configured such that the outer movable strut 142 can move up and down with respect to the inner fixed strut with a stroke of, for example, 270 mm in the height direction.
  • the elevator 141 incorporates a drive mechanism such as a DC motor and a height sensor.
  • the movable strut 142 is provided with a drive unit DV having a rotation mechanism similar to the rotation drive mechanism 83 described above.
  • the drive unit DV includes support plates 143 and 144 projecting from both side surfaces of the upper portion of the movable support column 142, and an electric motor 145 with a gear box with electromagnetic brakes disposed on the support plates 143 and 144, respectively. 146.
  • the drive unit DV includes a rotation drive mechanism 147 provided through the upper part of the movable support column 142 in the front-rear direction (Z-axis direction) orthogonal to the projecting direction of the support plates 143 and 144.
  • the end portion on the front side of the rotation drive mechanism 147 protrudes from the movable column 142, and the support portion 21L of the X-ray tube arm 21 and the support portion 22L of the detector arm 22 described above are provided on the protruding portion. It is attached coaxially.
  • an end portion on the rear surface side of the rotation drive mechanism 147 also protrudes from the movable column 142, and two speed reducers 148 and 149 are coaxially attached to the protruding portion.
  • Each of the motors 145 and 146 is a stepping motor, and includes gear boxes 145A and 146A on the output shaft side. These gear boxes 145A and 146A are linked to the speed reducers 148 and 149 via belts 150 and 151, respectively. Yes.
  • the rotation drive mechanism 147 incorporates a known shaft mechanism that transmits rotation independently from each other inside and outside by a bearing or the like. For this reason, two shafts inside and outside the shaft mechanism are linked to the support portion 21L of the X-ray tube arm 21 and the support portion 22L of the detector arm 22, respectively.
  • the rotation of the X-ray tube rotation motor 145 causes the X-ray tube arm 21 to rotate in the circumferential direction as described above, and the rotation of the detector rotation motor 146 similarly causes the detector arm 22 to move in the circumferential direction. Rotate.
  • Their rotation direction, rotation speed, and rotation range can be controlled independently of each other by controlling the driving of the two motors 145 and 146 separately.
  • An electric motor 152 with a gear box for rotating the opposing arm portions 21A and 22A at the distal ends of the support portion 21L for the X-ray tube and the support portion 22L for the detector provided as the arm portion AM. , 153 are provided. These electric motors 152 and 153 are stepping motors, and their output shafts are linked to the opposing arm portions 21A and 22A on the X-ray tube side and the detector side, respectively. For this reason, the rotation movements of the electric motors 152 and 153 can control the above-described rotational motions of the opposing arm portions 21A and 22A on the X-ray tube side and the detector side, that is, the X-ray tube 23 and the detector 24, independently of each other. It has become.
  • the four-axis rotation operation described above can be independently controlled by the mechanism according to this modification, and the above-described scan control can be performed.
  • the X-ray tube 23 and the detector 24 are always facing each other while moving independently on different circular orbits.
  • attitude control of four axes that is, partial revolution and rotation of the X-ray tube 23 and partial revolution and rotation of the detector 24
  • the apparatus can be miniaturized and the degree of freedom in designing the X-ray path is extremely high.
  • the trajectory of the X-ray path is arbitrarily determined so that a desired image can be taken.
  • the X-ray tube 23 and the detector are arranged around two identical orbits around the same central axis CA passing through one rotation center O and having different distances (diameters) from the central axis CA. 24 are rotated (revolved) independently of each other.
  • the X-ray tube 23 and the detector 24 are rotated (rotated or swung) around the first and second axes AXs and AXd parallel to the rotation axis CA at the respective rotation positions. it can. That is, since both the X-ray tube 23 and the detector 24 can rotate (attitude control), they can always maintain a state of facing each other.
  • the X-ray tube 23 and the detector 24 are relatively simple and can be reduced in size by rotating on their respective circular orbits.
  • the fan beam-shaped X-ray path can be drawn from various angles in the imaging space S and can be easily changed. For this reason, various focal planes can be set in the imaging space S.
  • the distance from the central axis CA to the X-ray tube 23 and the detector 24 is different. That is, the detector 24 can be rotated at a position as close as possible to the imaging region JW of the subject P.
  • the focal spot size (0.15 mm in this embodiment) of the X-ray tube 23 is the same, the magnification rate increases and the resolution increases as the detector 24 approaches the subject P. Detection accuracy is also improved.
  • the X-ray XB irradiated from the X-ray tube 23 is always limited to the size of the X-ray incident window WD of the detector 24.
  • the X-ray tube 23 and the detector 24 are driven and controlled independently by the four axes, and both are always opposed to each other via the jaw of the subject P during scanning. For this reason, the X-ray XB irradiated from the X-ray tube enters the detector 24. Therefore, the amount of scattered radiation leaking from the imaging space S is small.
  • X-rays focused in a fan beam shape having a rectangular opening rotate around the central axis CA, the amount of scattered radiation leaking in the front-rear direction of the imaging space S is further reduced.
  • a control board (not shown) on which the circuit of the console 15 shown in FIG. 9 is mounted is arranged in the space US on the upper surface of the tower unit TW.
  • the power supply box 13 that forms the base portion BS is equipped with only a converter that converts the voltage from AC 100V to DC 24V, and only a cable that sends the DC output to the control board or the electric motor is routed. For this reason, compared with the case where this control board is placed in the power supply box 13, wiring is also simplified.
  • the translucent portion 14TR formed on the cover 14C may be an appropriate rectangular translucent window 14TR ′ provided on both side surfaces as shown in FIG. 17 instead of the shape of FIG. 5 described above.
  • the translucent window 14TR ′ is formed of a resin material containing lead, and the other non-translucent portion 14NT is formed of a metallic plate material. Also by this, the effect of shielding the scattered radiation can be expected, and the entire weight can be reduced by reducing the lead-containing portion.
  • This translucent window 14TR ′ is primarily capable of observing the state of the patient by the dentist during scanning, and it is better if the discomfort of the patient who is not good at closing can be reduced.
  • the shape of the translucent window 14TR ′ is not limited to a rectangle, but may be a slit, a circle, or a triangle. Further, the translucent window 14TR ′ may be provided only on one side surface of the cover 14C. The position in the height direction of the translucent window 14TR ′ is usually set so that a dentist who performs a scanning operation in a standing position can observe the head of the patient inside through the translucent window 14TR ′.
  • the X-ray panoramic imaging apparatus has a more specific configuration of the teaching function outlined in the first embodiment.
  • this teaching function includes a standard imaging method and an orthogonal imaging method along the standard trajectory SS on the dentition TR that is the trajectory of the 3D reference tomographic plane. In addition to or can be carried out alone.
  • FIG. 13 shows the geometrical relationship when the film FM is inserted into the subject's mouth and irradiated with X-rays from the outside.
  • film FM is placed at a position where the target teeth are photographed, and is photographed in a state where it is held with a finger or the like.
  • the dentist images the X-ray irradiation angle at the time of imaging while adjusting the direction of the cone CN of the external X-ray irradiator. That is, the optimum X-ray incident angle for photographing the target tooth is confirmed in a simulated manner.
  • the SID distance between the X-ray focal point and the film
  • the panoramic imaging apparatus 1 intends to achieve this dental X-ray imaging function based on the above-described 4-axis independent control. What is needed at this time is a teaching function.
  • the precision photographing according to this embodiment will be described with reference to FIG.
  • a region 50 mm (25 mm + 25 mm) including this back tooth is the imaging range.
  • the actual captured image has a rectangular shape of about 50 ⁇ 50 mm. Therefore, the detector 24 is located outside the right cheek, and the X-ray tube 23 is located outside the left cheek on the opposite side.
  • the detector 24 has a small number of pixels in the horizontal width direction and is regarded as a substantially vertical line sensor, the X-ray tube 23 and the detector 24 are simulated while being along the two trajectories Tx and Td. Are translated in opposite directions.
  • Frame data output from the detector 24 during this parallel movement is synthesized by the tomosynthesis method, and a precision photographed image of about 50 ⁇ 50 mm is obtained. This partially photographed image replaces an image obtained by a conventional dental X-ray.
  • teaching of the optimum X-ray irradiation angle is performed on the target tooth in advance using the teaching arm 25 described above.
  • the dentist can set the X-ray irradiation angle at the time of imaging while simulating the X-ray irradiation angle passing through the target tooth through this teaching.
  • the illustration of the X-ray tube arm 21 and the detector arm 22 is omitted.
  • the teaching arm 25 is L-shaped and has a substantially round bar shape, and its base is fixed to the rotation mechanism 170. For this reason, this teaching arm 25 can be rotated (rotated) around the face of the subject P (see arrow F1 in the figure).
  • the rotation mechanism 170 is provided with an encoder 171, detects the rotation angle of the entire teaching arm 25 (hereinafter referred to as the arm rotation angle ⁇ 1), and outputs a detection signal to the CPU of the controller 133 of the console 15. Is done.
  • the teaching arm 25 is a rod-like arm that is formed in an L shape as a whole, and includes a base side arm portion 25A and a tip side arm portion 25B.
  • the base side arm portion 25A extends to a part in the Z-axis direction, and the distal end side arm portion 25B is rotatably connected to the end portion of the arm portion.
  • the distal end side arm portion 25B extends in the Z-axis direction, and the end portion on the distal end side reaches above the jaw portion JW of the subject P.
  • the distal end portion of the base side arm portion 25A incorporates a rotation mechanism 172 that rotatably supports the distal end side arm portion 25B at the distal end portion, and an encoder 173 provided therewith. For this reason, when the front end side arm portion 25B is twisted, it can be rotated (turned) with respect to the base side arm portion 25A. This amount of rotation is also detected by the encoder 173, and the detection signal is sent to the CPU of the controller 133.
  • a small laser oscillator 181 and a push button switch 182 are provided at predetermined positions on the distal end side of the distal end side arm portion 25B.
  • the laser oscillator 181 can irradiate a laser beam LB toward the dentition TR of the subject P from the side surface on the distal end side of the arm.
  • the push button switch 182 is provided at the distal end of the distal arm portion 25B and can be pressed by a dentist. This switch signal is sent to the CPU of the controller 133.
  • the dentist can grasp the distal end side arm portion 25B of the teaching arm 25 and rotate it to irradiate the beam to a desired position of the dentition TR and confirm the position. Further, the irradiation angle of the laser beam can be changed by twisting (rotating) the distal end side arm portion 25B.
  • the incident angle of the laser beam LB that is, the irradiation angle of the actually irradiated X-ray beam XB (by changing the twist angle of the distal arm portion 25B) That is, the swing angle ⁇ 2) can be changed (see FIG. 16).
  • the laser oscillation point PT of the laser oscillator 181 is configured to be able to rotate on the same circular orbit as the X-ray focal point FP of the X-ray tube 23 described above. For this reason, the laser beam LB emitted from the laser oscillator 181 can simulate the X-ray beam XB at the time of actual imaging. For this reason, at the time of teaching, the X-ray tube arm 21 and the detector arm 22 are positioned at their standby positions so as not to disturb the manual teaching operation of the dentist. This retracted position is set to a position obliquely below the head of the subject P that is outside the teaching range.
  • step S11 the controller 133 first attempts to read the output signals from both encoders 171 and 173, and determines whether or not the arm rotation angle ⁇ 1 has been input (step). S12, S13). The dentist determines the desired arm rotation angle ⁇ 1 and swing angle ⁇ 2, and presses the push button switch 182. In response to this, the controller 133 can assume that the arm rotation angles ⁇ 1 and ⁇ 2 have been determined (step S14, YES). If this determination is NO, since the dentist is still in a trial and error stage to determine the arm rotation angle ⁇ 1, the process returns to step S2 and waits while repeating the processes of steps S12 to S14.
  • Step 15 displays the arm rotation angle ⁇ 1 and the swing angle ⁇ 2 determined in a simulated manner on the display 136 (or a portable monitor at hand). If the dentist does not agree with the display result, the process returns to step S12, and the arm rotation angle ⁇ 1 and the swing angle ⁇ 2 are set again (NO in step S16).
  • step S16 if the angles ⁇ 1 and ⁇ 2 set by the dentist are agreed (step S16, YES), the speed for translation in the opposite direction of the X-ray tube 23 and the detector 24 based on the angles ⁇ 1 and ⁇ 2 A pattern is calculated as control data (step S17).
  • the calculated control data is sent to and stored in, for example, the first storage unit 134 (step S18).
  • step S17 the algorithm for calculating the speed pattern (control data) executed in step S17 will be described with reference to FIG. In the figure, it is assumed that the tooth number 3 in the tooth row TR is the target tooth.
  • the midpoint of the line connecting the X-ray tube focal point and the detector surface at the oblique line at the position of the tooth number 3 and the intersection of the oblique line and the dentition ellipse TR are calculated. Although two intersection points are obtained, the intersection point closer to the detector 24 is adopted.
  • the slanted line indicates a line of the swing angle ⁇ 2 at the arm rotation angle ⁇ 1 simulated by the laser beam. The detector 24 always moves in front of the subject.
  • the X-ray tube 23 and the detector 24 on the orbital circles Ts and Td during imaging trajectory control are divided into a range from the start position to the teaching position and a range from the teaching position to the end position, respectively.
  • the position is calculated for both the X-ray tube 23 and the detector 24, and the above-described velocity pattern is calculated so that the X-ray tube 23 and the detector 24 face each other at the respective positions.
  • the speed pattern of the 4-axis independent control of the X-ray tube 23 and the detector 24 set in this way is output as control data.
  • the teaching device is configured with the processing of the controller 133, the first storage unit 134, the rotation mechanisms 170 and 172, the encoders 171 and 173, the laser oscillator 181 and the push button switch 182 as main parts. And integrated into the panoramic photographing apparatus 1.
  • the teaching device since the teaching device is integrated in the panoramic photographing device 1, it is advantageous in that the panoramic photographing device 1 can use the teaching control data as it is.
  • the panoramic photographing apparatus 1 When using the panoramic photographing apparatus 1 according to the present embodiment, first, the panoramic photographing apparatus 1 is positioned at a predetermined position on the back side of the dental treatment chair 2 and fixed to the floor surface. At this time, the operation lever 52 described above is operated to push the pin 50 down, and the pin 50 is engaged with the floor fixing portion 53. Thereby, positioning and fixation with respect to the dental treatment chair 2 of the main body BD of the panoramic imaging apparatus 1 are achieved.
  • the scattered radiation shielding cover 14C is retracted to the rear side (see the imaginary line “retraction position” in FIG. 3).
  • the X-ray tube arm 21 and the detector arm 22 are positioned at their initial positions. Therefore, the dentist positions the head H of the patient P at a predetermined position in the imaging space S while tilting the backrest of the dental treatment chair 2. This positioning is performed by adjusting the height direction of the elevator 14 and positioning the midline, Frankfurt, and canine by three laser beams (not shown).
  • the scattered radiation shielding cover 14C is moved to the imaging position in the forward direction (see the solid line “imaging position” in FIG. 3).
  • the head H of the subject P is positioned in the defined imaging space S.
  • the scattered radiation shielding cover 14C is empty, and the X-ray tube arm 21 and the detector arm 22 are retracted.
  • the above-described teaching is performed to set control data for precisely photographing a desired imaging range.
  • the scattered radiation shielding cover 14C is closed and the apparatus 1 is operated in the same manner.
  • the velocity pattern set as the control data is an attitude in which scanning is performed in a state in which the X-ray tube 23 and the detector 24 face each other in some specified ranges of the trajectories Tx and Td of the detector 24, respectively.
  • Control data For this reason, during scanning, X-ray irradiation is executed only in those designated ranges, and data collection in a partial designated range is executed.
  • the collected frame data is synthesized using the tomosynthesis method to obtain a precision photographed image similar to a conventional dental X-ray. Therefore, the discomfort and inconvenience of both the patient and the dentist when using the conventional dental X-ray can be solved.
  • partial X-ray imaging aiming at several teeth can be performed.
  • the center position of the imaging range is designated, and the incident direction of the X-ray beam in which the overlapping of teeth in the region is eliminated as much as possible is designated.
  • the imaging range of the dentition can be determined from a predetermined length.
  • the command values for the X-ray imaging range and the incident angle of the X-ray beam can be simulated in advance with a laser beam before actual scanning, and the command values (control data) can be set accurately. This command value is reflected in actual X-ray imaging.
  • the teaching according to the third modification is a simple method that does not necessarily require the teaching arm 25 to be used.
  • this method as shown in FIG. 10, assuming that the dentition TR of the subject P draws a standard trajectory SS, the rotation angle ⁇ in the circumferential direction of each tooth (target tooth) constituting the dentition TR is shown. The position of is fixed. Therefore, a speed pattern can be calculated and stored in advance based on the algorithm of FIG. 18 described above for each target tooth. In this case, for each of the maxillary and mandibular teeth arranged along the standard trajectory SS, the corresponding rotation angle ⁇ is determined, the direction orthogonal to the teeth is determined, for example, and the speed pattern is calculated from the angle and direction. is there.
  • a table in which the tooth number and the speed pattern are associated with each other may be stored in the first storage unit 134, for example.
  • one set of velocity patterns is composed of four velocity patterns by revolution and rotation of the X-ray tube 23 and the detector 24.
  • tooth numbers, a plurality of X-ray incident angles on each tooth, and a plurality of sets of velocity patterns corresponding to each tooth and each X-ray incident angle may be prepared.
  • FIG. 25 illustrates a set of speed patterns for partial shooting for adults that are actually calculated.
  • 2 shows a speed pattern (curve B ′), a rotational speed pattern (curve A ′) of the X-ray tube 23, and a speed pattern (curve B ′ showing partial rotation) of the X-ray tube 23 of the detector 24.
  • FIG. 4B shows a set of similar speed patterns for the “left, lower jaw, and number 7” teeth.
  • the above-mentioned speed pattern data only needs to designate on the GUI screen of the display 136 the target tooth that the dentist wants to diagnose at the time of partial imaging.
  • the controller 133 reads a set of operation patterns shown in FIG. 25A from the first storage unit 134,
  • the partial imaging of the target tooth can be performed according to the procedure shown in FIG.
  • This partial imaging that is, a partial area centered on the target tooth may be scanned (partial scan), and the frame data collected thereby may be reconstructed with a predetermined profile of the shift and add amount.
  • a partial captured image similar to that of a conventional dental X-ray can be obtained.
  • a partial captured image can be obtained by designating only the target tooth, so that the labor of the dentist is reduced and the X-ray exposure is reduced.
  • the reason why such a simple partial photographing can be adopted is that the patient's dentition is often along the standard trajectory SS although there are individual differences.
  • the top surface, both side surfaces, and the bottom surface that define the imaging space S are surrounded by the above-described scattered radiation shielding cover 14C and the scattered radiation shielding plate 20 of the bottom surface portion 14C, and are subjected to X-ray shielding. ing. For this reason, X-rays leaking outside from the imaging space S during panoramic imaging or partial imaging can be reliably reduced or shielded. Thereby, even when panoramic imaging or partial imaging driven by the X-ray tube 23 is performed, the influence of X-rays on the outside of the imaging space S can be almost ignored.
  • This panoramic photographing apparatus 1 is movable. Therefore, it is possible to provide a panoramic imaging apparatus having an X-ray shielded space that should be called a “portable dental X-ray shield room”. Thereby, X-ray imaging
  • photography of a jaw part can be performed with the patient lying in the dental treatment chair on its back. Leakage to the outside from a very localized small imaging space around the jaw during the imaging can be greatly reduced.
  • the head H is put in the scattered radiation shielding cover 14C, and the translucent portion 14TR is provided in the cover 14C. For this reason, the outside can always be seen, and even patients who are not good at closing can be handled.
  • the caster 11 is provided as a moving means for moving the main body BD (excluding the console) of the apparatus 1.
  • this moving means is not limited to casters.
  • a gripping portion may be provided on the main body of the apparatus 1, and the gripping portion may be held and moved by hand.
  • you may provide the wheel which rotates electrically on the lower surface of the base part 12.
  • FIG. Any means capable of freely moving the main body BD of the apparatus 1 according to the present application to the side of the dental treatment chair 2 may be used.
  • a scattered radiation shielding plate (third shielding body) 31 made of a lead plate is fixedly arranged inside the back surface portion 14B of the elevator 14. At this time, it is convenient to make a hole in the scattered radiation shielding plate 31 so as to avoid the portion of the rotation center axis C such as a motor. This also gives the scattered radiation shielding function to most of the back side.
  • a warm X-ray protective curtain (fourth shield) 32 is also suspended from the vacant front surface (front surface) of the scattered radiation shielding cover 14C.
  • the scattered radiation shielding cover 14 ⁇ / b> C originally has little scattering of scattered radiation (the same applies to the back side), but as a further countermeasure against scattered radiation, the front is also subjected to X-ray shielding.
  • the X-ray protective curtain 32 is formed by connecting, for example, a plurality of strip-shaped portions in which lead is contained in a flexible resin and has an X-ray shielding function. A portion of the X-ray protective curtain 32 that corresponds to the neck portion of the subject is cut out in a substantially semicircular shape along the shape.
  • the X-ray shielding wall part that separates the imaging space S from the outside world is composed of all six surfaces including the front and back surfaces as schematically shown in FIG. Will cover.
  • the scattered radiation leaking out from the imaging space S at the time of imaging can be further reliably reduced, and the scattered radiation shielding function described above is further strengthened. Therefore, the influence of X-rays on the outside of the imaging space S due to imaging can be almost ignored, and the reliability of X-ray protection can be further enhanced. Of course, this is the same even when the X-ray shielding means of either FIG. 26 or FIG. 27 is adopted.
  • the X-ray protective curtain 32 may be a single plate made of a resin plate containing lead.
  • This X-ray panoramic imaging apparatus 1A includes a side handle 55 for conveyance on both sides of the apparatus in addition to the same configuration as the X-ray panoramic apparatus shown in FIG.
  • the moving handle 54 is also provided on both sides as shown in FIG.
  • a multipurpose storage rack 56 and a monitor 57 indicating the operating state of the apparatus 1A can be detachably attached to one of the two side handles 55.
  • the storage rack 56 can store a terminal such as a dentist PC for inputting patient information or the like to the apparatus 1.
  • These terminals and the monitor 57 can communicate with a control circuit (not shown) disposed inside the console 15 or the power supply box 13 by, for example, wireless communication.
  • an irradiation switch 58 for instructing X-ray irradiation and rotation of the X-ray tube / detector via a cord 58C having a length of 2 m, for example, is provided on the back surface portion 14B.
  • a positioning element having functions equivalent to those of the fixing pin 50, the cover portion 51, and the floor fixing portion 53 shown in FIG. Specifically, as shown in FIG. 29, a positioning mechanism unit for stopping and positioning the position of the panoramic imaging apparatus 1A on the side of the dental treatment chair 2 at the front end of the pedestal unit 12 of the main body BD. 61 is provided.
  • the positioning mechanism 61 includes a stop pin 62 and a positioning pin 63 which will be described later.
  • the positioning pin 63 moves up and down in conjunction with an operation lever 52 (see FIG. 30) provided on the upper edge of the back surface part 14B via a wire mechanism described later.
  • a substantially triangular shape can be formed in a side view, and the abutment pin 62 can be contacted, and a positioning pin 63 can be inserted.
  • a floor fixing portion 71 having a hole is fixed. For this reason, if the apparatus main body BD is moved, the tip position thereof is aligned with the position of the floor fixing portion 71, and the operation lever 52 is operated with the stop pin 62 in contact with the floor fixing portion 71.
  • the positioning pin 63 can be pushed down.
  • the apparatus main body BD is positioned at a predetermined position with respect to the dental treatment chair 2 as in the positioning state shown in FIG.
  • the operation lever 52 is operated to raise the positioning pin 63.
  • apparatus main body BD can be released from position fixing with floor fixing
  • a rear handle 54 is fixed to the upper end portion of the rear portion 14B so as to be positioned on both sides of the operation lever 52. For this reason, the operator can easily move the apparatus main body BD by freely rotating the caster 11 by pulling and pushing the two rear handles 54.
  • this apparatus main body BD is provided with a substantially inverted U-shaped side handle 55 that is fixed at one end on the bottom surface of the pedestal portion 12 and rises vertically from the side.
  • the side handle 55 is formed of a metal pipe, for example.
  • a guide pole 59 for a guideline is attached to a position on the side surface of the power supply box 13 below the back surface portion 14B while being suspended toward the floor F as shown in FIG.
  • the tip of the reference pole 59 on the floor surface side is close to the floor surface F.
  • a guideline GL made of tape, paint, or the like arranged on the floor surface F is laid on the floor surface F toward the floor fixing portion 71 described above. Therefore, when the apparatus main body BD is moved toward the floor fixing portion 71, that is, toward the dental treatment chair 2, the apparatus main body BD can be easily moved by pushing the tip of the guide pole 59 so as to follow the guideline GL. In addition, the dental treatment chair 2 can be easily accessed.
  • the stop pin 62 comes into contact with the predetermined surface of the floor fixing portion 71 and stops, the positioning pin 63 is driven by operating the operation lever 52 described above to achieve the positioning described above.
  • the X-ray shielding room (that is, the device 1A) can be easily carried to an arbitrary place by the caster 11 by grasping and pushing the back handle 54 and can be used there.
  • ⁇ Positioning mechanism> A positioning mechanism for positioning the panoramic imaging apparatus 1A with respect to the dental treatment chair 2 will be described.
  • this positioning mechanism is provided in the panoramic photographing apparatus 1A itself, but also includes a positioning floor fixing unit 71 fixed to the floor surface F.
  • the elevator 14 of the panoramic photographing apparatus 1 ⁇ / b> A has an operation lever 52 fixed to a predetermined portion on the upper edge of the back surface portion 14 ⁇ / b> B, and a lever drive for supporting and driving the operation lever 52. Part 81.
  • the operation lever 52 is provided for the operator to manually tilt and fix the position of the panoramic photographing apparatus 1A.
  • the lever driving portion 81 includes a support shaft 82 erected at the predetermined portion and a rotation shaft 183 pivotally supported by the support shaft 82. And have.
  • An operation lever 52 is fixed to the rotating shaft 183. For this reason, if the operating lever 52 is grasped and rotated, the rotating shaft 183 also rotates integrally.
  • a hole HL for inserting a hand is opened in the upper part of the operation lever 52 so as to be easily gripped, but an inflating part 52A that swells round in a side view is partially formed in the lower part thereof.
  • the inflatable portion 52A is in contact with a ball plunger 84 provided upright at the predetermined portion.
  • the ball plunger 84 is locked to the operation lever 52 at positions where the angle of the operation lever 52 is 0 ° (horizontal), 45 °, and 90 ° (vertical), and when the tilting power is applied more than a certain level, It is possible to rotate between.
  • the lever driving portion 81 has first and second links 85A and 85B provided on one end side of the rotating shaft 183.
  • One end of the first link 85A is fixed to one end of the rotating shaft 183.
  • the first link 85A swings as the rotation shaft 183 rotates.
  • One end of the second link 85B is fixed or rotatable to the other end of the first link 85A, and converts the swing motion of the first link 85A into a reciprocating motion.
  • a wire 86 is connected to the other end of the second link 85B.
  • the operation lever 52 is erected in an initial position P1 (90 ° tilt position), and an intermediate position P2 tilted forward from the position P1 (45 ° tilt position). Further, it is possible to take a three-stage operation position called a fixed position P3 (a tilt position of 0 °) tilted further forward from the position P2, and to lock each operation position with a certain resistance. On the contrary, the operation lever 52 can be returned in the order of positions P3, P2, and P1. The operator operates the operation lever 52 while resisting a certain resistance by the ball plunger 84, and when a position P1, P2, P3 is reached, a click feeling is obtained, and at that position, a certain resistance is applied. Locked.
  • the wire 86 is loosely inserted inside the sheath SF.
  • the sheath SF is fixed and piped inside the elevator 14 so as to avoid the internal mechanism and to form a linear path as much as possible. For this reason, the wire 86 moves in the directions indicated by arrows A and B in FIG.
  • the tip of the wire 86 reaches the tip on the front side of the pedestal portion 12 and reaches the inside of the pin cover 91 that is fixedly extended to the tip.
  • the pin cover 91 is fixed to the distal end portion of the pedestal portion 12, and projects from the distal end side by a certain distance in a bowl shape (see FIGS. 29 and 32).
  • the positioning mechanism 61 includes the stop pin 62 and the positioning pin 63 described above.
  • the step portion 92A of the support portion 92 is integrally provided with substantially rectangular parallelepiped protrusions 92B at both ends in the lateral direction, that is, in the X-axis direction.
  • the step portion 92A is provided with four guide holes H1, H2, H3, and H4 in a line along the lateral direction.
  • guide holes H1 and H4 at both ends are guide holes for guiding the positioning pin 63 in the vertical direction.
  • the guide holes H1 and H4 penetrate the stepped portion 92A and the protruding portion 92B in the vertical direction.
  • positioning pins 63 are held and accommodated in the guide holes H1 and H4, respectively, and can move up and down along the guide holes H1 (H4).
  • the positioning pin 63 is, for example, a metal cylindrical rod having a predetermined diameter, and has an annular protrusion 63A in the middle in the vertical direction.
  • annular protrusions HT1 and HT2 are respectively provided at the positions of the upper and lower ends of the guide hole H1 (H4) in the vertical direction. Therefore, as shown in FIG. 34, the distance L1 between the projection 63A in the middle of the pin 63 and the projection HT2 at the lower end of the guide hole H1 (H4) is set as the movable range in the vertical direction of the positioning pin 63. Yes.
  • a coiled spring 93 is inserted in a space between the protrusion 63A of the positioning pin 63 and the protrusion HT1 on the upper end side of the guide hole H1 (H4).
  • the pin 63 takes the initial position Q1 indicated by the solid line in FIG.
  • This initial position Q1 is obtained by a “large” pulling force acting in the direction indicated by the arrow B described above when the operation lever 52 is at the initial position P1 (90 ° tilt position).
  • the upper end of the positioning pin 63 is flush with the upper surface of the projecting portion 92B of the support portion 92, and the lower end is almost flush with the lower surface of the stepped portion 92A. That is, the positioning pin 63 is accommodated in the guide hole H1 (H4).
  • the positioning mechanism portion 61 is a mechanism for moving the two positioning pins 63 up and down in accordance with the movement of the wire 86.
  • the tops of the two positioning pins 63 are rigidly connected to the suspension shaft 63C.
  • the suspension shaft 63 ⁇ / b> C of both the pins 63 is fixed to the lateral arm 101 that is laterally mounted in the lateral direction, that is, the X-axis direction.
  • the horizontal arm 101 is pivotally supported by two rings 102 at predetermined positions on both ends thereof. Further, the two rings 102 are supported by the two arms 103 so as to roll along the upper surface thereof.
  • the two arms 103 are rigidly connected to a single link 104, and the link 104 is rigidly connected to the rotating arm 105.
  • the rotating arm 105 is further coupled to the wire 86 described above via a connecting body 106.
  • the guide holes H1 and H4 described above are formed with a slit-like opening OP over a predetermined length from the upper end side of the guide holes H1 and H4 in order to allow the horizontal arm 101 to move in the vertical direction. (See FIG. 33).
  • the guide holes H1 and H4 is provided with three hall sensors 111A, 111B, and 111C so as to be slightly recessed from the inner surface.
  • the three hall sensors 111A to 111C are detection means for detecting the vertical movement of the positioning pin 63. Therefore, the positions of the three hall sensors 111A to 111C in the vertical direction, that is, the Y-axis direction are respectively the distances of an initial position Q1, a first-stage descending position Q2, and a second-stage descending position Q3, which will be described later. Correspondingly, the distance is set to be the same.
  • the two lower positions Q2 and Q3 other than the initial position Q1 are positions determined by the lower end of the positioning pin 63 being restricted by the bottom of the two-stage groove and hole described later of the floor fixing portion 71 by the extension of the spring 93. It is.
  • a magnet 112 is embedded in the outer peripheral surface of the positioning pin 63 so as to face the uppermost hall sensor 111A at the initial position Q1.
  • the Hall sensor 111A is positioned in the magnetic flux generated from the magnet 112, so that the Hall sensor 111A generates a voltage and outputs the voltage signal.
  • the hall sensors 111A to 111C send voltage signals to the control circuit of the power supply box 13 described above via lead wires (not shown).
  • each of the two stop pins 62 includes a fixing member 62A, and the fixing member 62A is fixed to the stepped portion 92A.
  • the heights of the lower ends of the two stopping pins 62 are kept constant.
  • the diameter of the guide hole H2 (H3) that accommodates the stop pin 62, that is, the diameter of each stop pin 62 is larger than that of the above-described guide holes H1, H4, that is, the positioning pins 63.
  • the reason is that the object body BD pushed by the operator is brought into contact with the floor fixing portion 71 and stopped before positioning, and it is necessary to have sufficient strength. It is necessary to prevent the apparatus main body BD from colliding with the dental treatment chair 2 due to inertia or the like.
  • the floor fixing portion 71 is a horizontally long member made of resin or metal, and is fixed to the floor surface F near the headrest when the backrest of the dental treatment chair 2 is tilted with screws or the like.
  • the floor fixing portion 71 is configured such that a cross section thereof in the horizontal direction, that is, the Z-axis direction here is shown in FIG.
  • a gentle slope 71A starts from the front end, and a long groove 71B dug shallowly along the longitudinal direction, that is, the X-axis direction in this case, lies at the back (see FIG. 35).
  • two positioning holes 71C that are further dug from the bottom surface are formed.
  • the interval between the two positioning holes 71C is the same as the interval between the two positioning pins 63 described above.
  • the long groove 71B follows the steep contact surface 71D with which the stop pin 62 can contact, and the contact surface 71D passes through the top portion 71E and falls to the back side, that is, the dental treatment chair 2 side and ends. .
  • the bending state of the contact surface 71D is made to match the curved shape of the distal end portion of the stop pin 62 as described above.
  • this control circuit includes a processor 120 constituted by a CPU.
  • the processor 120 turns on / off the red, yellow, and blue LEDs 121A, 121B, and 121C depending on which Hall sensor has an output signal and the detection state thereof.
  • These LEDs 121A, 121B, and 121C are installed, for example, at the upper end portion of the back surface portion 14B of the main body BD.
  • the processor 120 turns on the red LED 121A and turns off the remaining LEDs 121B and 121C.
  • the processor 120 when receiving an output signal from the second hall sensor 111B, the processor 120 turns on the yellow LED 121B and turns off the remaining LEDs 121A and 121C. Similarly, when an output signal is received from the third hall sensor 111C, the blue LED 121C is turned on and the remaining LEDs 121A and 121B are turned off.
  • the panoramic photographing apparatus 1A according to the present embodiment is configured as described above. For this reason, various effects are exhibited as described below.
  • this panoramic photographing apparatus 1A is configured to be portable, it can be easily moved by a dentist or a nurse.
  • the dentist or nurse holds the back handle 54 and pushes the apparatus 1A while keeping the guide pole 59 along the guideline GL. That's fine.
  • the tip of the guide line GL reaches the center position C in the longitudinal direction of the floor fixing portion 71 on the floor surface F (see FIG. 35). This center position C is matched with the lateral center position of the headrest when the backrest of the dental treatment chair 2 is tilted.
  • the device is further advanced while reducing the pressing speed slightly. Accordingly, the two stop pins 62 discharged from the lower surface of the positioning mechanism portion 61 by the predetermined height L2 come into contact with the contact surface 71D of the floor fixing portion 71. Since the floor fixing portion 71 is fixed to the floor surface F, the panorama photographing apparatus 1A also stops when it comes into contact with the contact surface 71D (see FIG. 32). At this time, the tips of the two positioning pins 63 are stored at the initial position Q1 (see FIG. 34), and are positioned directly above the long groove 71B of the floor fixing portion 71. At this time, since the red LED 121A is lit by the output signal of the first hall sensor 111A, it can be notified that the positioning has not been performed yet.
  • the operator tilts the operation lever 52 from the initial position P1 to the intermediate position P2.
  • the wire 86 is pushed (loosened) and the turning arm 105 is also rotated forward (see FIG. 32, arrow A), the spring 93 has excellent elastic force, and the two positioning pins 63 are moved downward. Pressed.
  • the two positioning pins 63 are dropped into the long groove 71 ⁇ / b> B of the floor fixing portion 71. That is, the lower end of the positioning pin 63 shifts from the initial position shown in FIG. 34 to the first-stage lowered position Q2.
  • the yellow LED 121B is turned on by the output signal of the second hall sensor 111B. This informs the operator that the positioning has not yet been done, but that the first stage of positioning has been completed.
  • the operator tilts the operation lever 52 from the intermediate position P2 to the fixed position P3.
  • the wire 86 is further loosened and the rotating arm 105 is further rotated forward (see arrow A in FIG. 32), and the two positioning pins 63 are further pushed downward.
  • the pins 63 are dropped into the positioning holes 71C as they are (FIG. 34). (Refer to the lower position Q3 of the second stage). In this lowered state, the positioning mechanism portion 61 is locked to the floor fixing portion 71 by the urging force of the spring 93.
  • the apparatus main body BD that is, the panorama photographing apparatus 1A is positioned by the position of the floor fixing unit 71. That is, the panoramic photographing apparatus 1A is positioned in a fixed state with respect to the dental treatment chair 2 at a predetermined position. At this time, since the output signal of the third hall sensor 111C becomes valid, the blue LED 121C is lit. Thereby, the completion of positioning is notified.
  • the tip ends of the two positioning pins 63 may be slightly displaced from the positions of the two positioning holes 71C.
  • the operator may hold the back handle 54 or the side handle 55 and slightly move the apparatus main body BD left and right. Thereby, a pin position that matches the position of the positioning hole 71C can be found. If the positions match, the operating lever 52 is already in the fixed position P2 and the urging force of the spring 93 is working, so the two positioning pins 63 automatically click into the two positioning holes 71C. Dropped and locked. That is, the positioning pin 63 changes from the first-stage lowered position Q2 to the second-stage lowered position Q3 shown in FIG. As a result, the blue LED 121C is lit and positioning is completed.
  • the scattered radiation shielding cover 14C is retracted to the rear side (see the imaginary line “retraction position” in FIG. 3).
  • the X-ray tube arm 21 and the detector arm 22 are positioned at their initial positions. Therefore, the dentist (or operator) positions the head H of the patient P at a predetermined position in the imaging space S while tilting the backrest of the dental treatment chair 2. This positioning is performed by adjusting the height direction of the elevator 14 and The laser beam is applied to the midline, the Frankfurt plane, the occlusal plane and the canine.
  • the scattered radiation shielding cover 14C is moved to the imaging position in the forward direction.
  • the head H of the subject P is positioned in the defined imaging space S.
  • the dentist presses the irradiation switch 58 from a position slightly away the panoramic imaging described above is activated and data is collected. This series of photographing procedures is the same as that described in the first and second embodiments.
  • the subject P is released from the imaging space S by opening the scattered radiation shielding cover 14C (retracted position) and returning the back of the dental treatment chair 2 to the original position.
  • the scattered radiation shielding cover 14C is closed (imaging position), and the panorama imaging apparatus 1A is moved to another location.
  • the operation lever 52 may be continuously returned to the fixed position P3, the intermediate position P2, and the initial position P1.
  • the wire 86 and the rotating arm 105 are returned (see FIG. 32, arrow B), and the positioning pin 63 returns to the initial position against the elastic force of the spring 93 and takes the initial position Q1.
  • the red LED 121A is turned on.
  • the apparatus main body BD is released from the floor fixing
  • the panoramic photographing apparatus 1A can be freely moved and can be reliably and accurately positioned with respect to the dental treatment chair 2.
  • the apparatus main body BD is surely stopped first using the stop pin 62, so that the subsequent positioning can be performed easily and quickly.
  • the operator can obtain a guide function using the guide pole 59 and the guide line GL, so that the operations up to positioning are facilitated.
  • the pin state until the positioning is completed can be monitored by the LED, the operator can improve the positioning work efficiency.
  • the various functions and effects described above can be similarly obtained in the embodiment.
  • the amount of scattered radiation that leaks in the front-rear direction of the imaging space S is very small, and X-ray shielding that should be called a “portable dental X-ray shielding room” is made.
  • the patient in the imaging space can be easily checked, and even patients who are not good at closing can be handled.
  • the operator uses the guideline GL and the guide pole 59 as a guide.
  • Various embodiments of the guide function are possible.
  • a plurality of intersecting lines GLs such as “long”, “medium”, and “short” intersecting with each other can be pasted at a predetermined position of the linear guideline GL.
  • the positioning pin 63 is set to be directly above the long groove 71B of the floor fixing portion 71 when the reference pole 59 reaches just above the shortest intersection line of the intersection line GLs.
  • the apparatus main body BD can be reliably positioned on the floor fixing portion 71.
  • a transmission / reception unit 131 that transmits and receives a medium such as a laser and an ultrasonic wave in a non-contact manner with the guide line GL may be provided in a part of the positioning mechanism unit 61.
  • the distance information to the floor fixing unit 71 can be known by voice or light.
  • a small camera 132 that photographs the front may be provided on the front surface of the positioning mechanism unit 61. This captured image may be displayed on a display (not shown) provided near the operation lever. According to these means 131 and 132, it is possible to reliably detect the front floor fixing portion 71 which is difficult to see, which greatly helps in positioning.
  • the hall sensor is provided as a sensor indicating the pushing state of the positioning pin 63, but this may be another sensor.
  • a non-contact sensor such as an optical sensor may be used, or a physical contact sensor may be used.
  • the installation position of the sensor is not necessarily limited to the above-described embodiment, and may be a place where the movement of the positioning pin 63 can be detected.
  • a non-contact sensor or a contact sensor can be embedded on the floor fixing portion 71 side, the arrival of the positioning pin 63 being pushed in can be detected, and the detection signal can be sent wirelessly to the apparatus body BD. Thereby, the detection operation equivalent to embodiment mentioned above can be performed.
  • the stop pin 62 in the panoramic photographing apparatus 1A described above may be employed.
  • the positioning pin also has a stopper function, and accordingly, a deformation such as increasing the diameter of the pin or increasing the number of pins to three or more is desirable.
  • the positioning hole 71C may be provided in the floor fixing portion 71. That is, a structure in which the long groove 71B is not formed may be employed.
  • the positioning pin 63 simply moves up and down in two stages.
  • the operation position of the operation lever 52 also takes the two-stage operation position of the initial position P1 (90 ° tilt position) and the fixed position P3 (0 ° tilt position) in FIG. For this reason, when the tip of the positioning pin 63 that has been lowered in response to the tilting operation to the fixing position P3 of the operation lever 52 is aligned with the positioning hole 71C, it is directly fitted into the hole 71C and locked. Is done.
  • the tip of the positioning pin 63 stops around the upper end of the positioning hole 71C.
  • the operator can find the positioning hole 71C by holding the back handle 54 or the side handle 55 and slightly moving the apparatus main body BD left and right.
  • the positioning pin 63 is automatically lowered by the elastic force of the spring 93, and is locked as described above.
  • the opening at the upper end of the positioning hole 71C may be slightly wider and tapered so that the diameter is reduced.
  • the number of positioning pins 63 is not necessarily two, and may be three or more. Further, when the two positioning pins 63 are provided as in the above-described embodiment, the distance between the pins may be separated and positioned at both ends in the width direction of the apparatus main body BD, that is, in the X-axis direction.
  • the positioning hole 71C may be directly formed in the floor surface F without providing the floor fixing portion 71 depending on the structure of the floor surface F.
  • a removable lid may be attached to prevent dust and the like from accumulating in the positioning hole 71C when not in use.
  • the above-described floor fixing portion 71 may be detachably attachable to the floor surface F.

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Abstract

La présente invention concerne un appareil d'imagerie panoramique à rayons X qui est muni d'un bras de tube à rayons X et d'un bras de détecteur, qui tournent de façon centrée sur un axe central (CA) indépendamment l'un de l'autre. Le bras de tube à rayons X est pourvu d'une section de logement de tube (21A), qui reçoit le tube à rayons X (23), et d'une section de support de tube (21L), qui porte ladite section de logement de tube de façon à pouvoir tourner autour d'un premier axe (AXs) qui est parallèle à l'axe central. Le bras de détecteur est pourvu d'une section de logement de détecteur (22A), qui reçoit le détecteur (24), et d'une section de support de détecteur (22L), qui porte la section de logement de détecteur de façon à pouvoir tourner autour d'un second axe (Axd) qui est parallèle à l'axe central. Pendant le balayage, les moyens d'entraînement respectifs sont commandés en fonction de modèles de vitesse de rotation indépendants l'un de l'autre. Il est possible d'enseigner les limites d'une imagerie partielle à l'aide d'un faisceau laser provenant d'un bras (25) qui simule un rayonnement réel de rayons X, et les résultats sont réfléchis dans des actions de commande à 4 axes. La présente invention concerne également un appareil d'imagerie portable comprenant un mécanisme pour empêcher des rayons X d'être diffusés à l'extérieur de l'espace d'imagerie, ou un mécanisme à positionner sur un fauteuil de traitement dentaire.
PCT/JP2015/052745 2014-02-21 2015-01-30 Appareil d'imagerie à rayons x WO2015125589A1 (fr)

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
JP2014-031911 2014-02-21
JP2014031911A JP2015156886A (ja) 2014-02-21 2014-02-21 Ｘ線撮影装置及び同装置に搭載される散乱線遮蔽装置
JP2014-035619 2014-02-26
JP2014035619 2014-02-26
JP2014037037A JP2015159973A (ja) 2014-02-27 2014-02-27 Ｘ線撮影装置
JP2014037568 2014-02-27
JP2014-037568 2014-02-27
JP2014-037037 2014-02-27

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EP3586751A4 (fr) * 2017-02-23 2020-11-04 J. Morita Manufacturing Corporation Dispositif de fluoroscopie à rayons x et procédé de tomographie à rayons x
CN112055562A (zh) * 2018-04-27 2020-12-08 株式会社森田制作所 X射线ct拍摄装置以及x射线ct拍摄装置的控制方法

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JP2001518341A (ja) * 1997-10-02 2001-10-16 プランメカ オイ 頭部ｘ線撮影装置
JPH11299773A (ja) * 1998-04-16 1999-11-02 Asahi Roentgen Kogyo Kk 可搬式横臥位対応型パノラマｘ線撮影装置
US6325538B1 (en) * 2000-03-17 2001-12-04 Christian M. Heesch Radiation field isolator apparatus
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WO2018095232A1 (fr) * 2016-11-22 2018-05-31 浙江思格一医疗科技有限公司 Dispositif de radioprotection léger
EP3586751A4 (fr) * 2017-02-23 2020-11-04 J. Morita Manufacturing Corporation Dispositif de fluoroscopie à rayons x et procédé de tomographie à rayons x
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CN112055562A (zh) * 2018-04-27 2020-12-08 株式会社森田制作所 X射线ct拍摄装置以及x射线ct拍摄装置的控制方法
CN112055562B (zh) * 2018-04-27 2024-03-01 株式会社森田制作所 X射线ct拍摄装置以及x射线ct拍摄装置的控制方法

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