JPS6053128A - Dental total jaw x-ray photographing apparatus - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention] This invention can be used not only in the dentition area but also in dental practice.

The present invention relates to a full-jaw XIII imaging device that can take panoramic photographs of the facial area, including oral functions and upper and lower jaws.

The above-mentioned dental full-jaw X-ray imaging device f that has been publicly announced
Most of the literature, patents, or utility models that describe methods for controlling the tomographic trajectory of the dentary curvature (hereinafter referred to as panoramic device) of II (hereinafter referred to as panoramic device) are Only means for moving the X-ray film receiving surface along an elliptical trajectory are discussed.

Therefore, if there are parts where the unique fault trajectory of the subject differs from the known orbit, accurate X-ray information can be obtained by blurring the different parts in the 111th cave panoramic photograph. First, there is a problem that the diagnostic accuracy decreases. In order to prevent this, the unique trajectory of any subject is made unknown, and a method for detecting this has been published and described in conjunction with the above control, that is, detecting the unique trajectory of the subject. The method is to use a matrix plate that can electrically detect the tooth alignment.
(1) Copying the dental electrotype with something like plaster or wax sheet, and obtaining the data of the dental electrostatic curve from them. Conventional devices that involve preprocessing operations for data collection not only complicate the operator's work and require an hour and effort, but also have the drawback of causing considerable pain to the subject. Furthermore, if the various dental alignment detection instruments described above are used repeatedly, it is necessary to sterilize and disinfect the instruments each time they are used for hygiene management reasons, which poses a problem that hinders the improvement of examination efficiency. .

This invention was made in view of the above-mentioned current situation, and is applicable to full-jaw photography using a conventional panoramic device.

This eliminates the drawbacks and problems of pretreatment operations using dental alignment testing instruments that have been used to improve diagnostic accuracy. That is, in a dental full-mouth X-ray imaging device, an ultrasonic probe and a detection circuit that controls the probe during imaging and detects the dental deposit layer trajectory unique to the subject in real time are used. A trajectory control circuit is provided in the image recording means, and also controls the image reception scanning speed in real time based on the output signal of the detection circuit, in other words, the tomographic trajectory signal, so as to enable imaging of a dental electrotomographic plane unique to the subject. The present invention relates to an apparatus characterized in that it is provided in an image receiving and scanning means. This configuration eliminates the need for detection equipment that comes into direct contact with the patient, which not only eliminates hygiene management problems and patient discomfort, but also allows the patient's unique trajectory of the dental deposits to be determined with great accuracy. The object of the present invention is to provide a convenient device that can detect and at the same time sharply photograph the tomographic plane of the trajectory with uniform density, has high diagnostic accuracy, and has excellent work efficiency.

Embodiments of the present invention will be described below with reference to the drawings.

FIG. 1 is a schematic (plan) view showing the structure of a dental full-mouth X-ray photographing apparatus using an X-ray film as an image recording means as a first embodiment of the present invention. X-ray tube as an X-ray source (]
)The X-ray film (2) serving as an image recording means is mounted, and the film drum (3) serving as an image receiving and scanning means which scans (rotates in this example) in the direction of the arrow (a1) is inserted into one line of the patient's cavity. (4) It is suspended on both ends of an arm (5) facing each other with w in between.The arm (5) has a Yuri friction roller (6) fixed to its upper part, and the central axis of this roller (6) (7) is provided at the center of a fixed solar friction wheel (8) having a friction transmission portion on its inner surface, and a shaft (9) is provided as a rotation-resistant center so as to be freely rotatable via an arm (6R), and the above-mentioned roller (6) is supported so as not to break its inscribed contact with the friction ring (8).In this mechanism, when the central axis (7) is given a single rotation in the direction of the arrow (111), the friction ring (6) The arm (5) fixed to the wheel (6) is shown by the dotted line (5a). position, and hold the arm (5
) and an X-ray tube (1) and a film drum (3
) take the positions (la) and (3a), respectively. As the rotation progresses further, the wheel (6) becomes (6b) and the arm (
5) comes to position (5b). In this rotation, the trajectory of the movement of the fixed point QOI (01) passing over the front of the tooth row (4) of the subject on the arm (5) is a pseudo-ellipse shape that closely resembles the front of the tooth row (4) as shown in the figure. The rolling wheels (6) and the friction wheels (8) are configured to form a continuous curve (pre-dental fault trajectory). For this purpose, the film drum (3) suspended from one end of the arm (5) continuously moves on a track (3K) in parallel along the front tooth row (4)K, thereby moving the film drum (3) to a certain point (101) on the arm. The relative relationship between the distance (Lm) of the focal point (IX) of the X-ray source with respect to the dental deposit trajectory 01) and the distance (Lb) of the film (2) with respect to the above-mentioned fault trajectory 01) is always constant. maintained.

And the arm (
XII which coincides with the central axis of 5)! Radiation beam (XE)
It is on the normal line passing through the center of the own vehicle with respect to the above-mentioned fault trajectory 0υ, that is, it rotates continuously while always orthogonally projecting the front tooth row (4). The main part of this invention is the X-ray entrance slit caused by the above-mentioned rotation of the film drum (3) f12
) The ultrasound probe (13) is placed at a position preceding the movement in the d1 direction, and the transmission and reception of ultrasound from this probe (13) is controlled to detect the subject immediately before imaging. and a pre-dental detection circuit that detects the individual's unique pre-dental tomographic trajectory (IIX).

Based on this detection signal, the arrow (al) of the film (2) is
This is a trajectory control circuit that controls the rotational (scanning) speed in the direction and photographs the individual tomographic plane.

Follow these fists to the station. #g2 Figure ■ is a front view of the side facing the X1fil source (11) of the film drum (3), and Figure 1 ■ is a front view of the side facing the X1fil source (11) of the film drum (3), and Figure 1 ■ is a front view of the film drum (3) with the ultrasonic probe 03) in positioning the subject. In Figure 2, which is a side view of the subject's head (14) showing the vertical positional relationship, the suspension arm 05)K engaged with one end of the arm (5) σ is the suspended film drum (3). The probe guide groove (17) provided on the right side of the slit 02) (close to and parallel to the slit 02) in the film drum rotating direction (DL side) is formed in the center of the front cover 06). 2)
It is formed in a structure that prevents X-rays from entering K, and the probe (
131 is supported so as to be movable up and down. Ultrasonic probe 0□□
□ is a piezoelectric vibrator made of lead zirconate titanate and a circular plate type or a concave convergence type with a diameter of about 8 to 10 mm, for example.

It is composed of an absorber made of rubber, for example, that absorbs unnecessary ultrasonic waves emitted from the back of the vibrator, and a substrate member that supports the vibrator and the absorber. For example, 2 MHz is determined depending on the thickness, and the thickness of the ultrasonic beam is determined by the above diameter. Describe the relationship.

The positioning operation is performed when the upper beam 09) of the two parallel light beams 081 (19) from the projector (not shown) provided in the device is shown in the figure below the orbital rim (a) +, l!
l: Adjust the head rest (not shown) so that it matches the eye-ear plane @ connecting the upper edge (21+) of the outer ear canal (not shown) inserted into both external ear canals.This adjustment The front tooth row (4) of the head Q41 is correctly positioned horizontally, and at the same time, the midline is determined by a mirror (not shown), completing the positioning of the deviation tj.At this time, the beam 09i is made parallel to the beam 09i, and its spacing is adjusted If the flexible lower beam 08) is aimed at the position in front of the patient's teeth (4), the beam (18) will be directed perpendicularly to the probe guide groove (19) of the film drum (3). As shown in (2), by aligning the center of the irradiated beam and the K probe (131), the positioning for emitting ultrasonic waves to the front of the subject's dentition (4) is completed.This positioning has been completed. When an ultrasonic pulse of, for example, 2 MI (z) is emitted from the ultrasound probe (13), for example, 2
Reflected waves (echoes) are returned from the interface between the two materials due to impedance mismatch. FIG. 3 is a time chart of the ultrasonic transmission and reception signals.

The vertical axis indicates the magnitude of the signal, and the 9th axis (tl indicates the passing of time, and now (Al), if it is a radiation signal, 0 is the echo at the interface between the probe and the air, and tel is the subject. The echo on the skin surface, ρ) is the echo on the outer surface of the dentary bone.

In (G), the echo 0 on the inner surface of the tooth row bone is an echo from the jawbone on the opposite side. These transmitted and received waveforms are generally based on the pulse reflection method called A mode, and the above echo 0. If the position of @ is known, the position of the unknown fault orbit (IIX) that exists in the center can be detected. Figure 4 v
Therefore, a basic circuit block diagram of the present invention will be shown for an embodiment of the apparatus which is connected to the station shown in FIG. 1 above. The ultrasonic transmission/reception control circuit (c) emits a radiation signal to the probe (13i) and controls the operation of the circuit (2) that processes the reflected signal received by the probe 031. The blocks (c) and (to) form the dentition curvature detection circuit, and the m force signal (a)) is the dentition acceptance signal.

This signal (a) and the output signal c1 of the 1 weighting coefficient setting circuit
The film drum rotation speed setting circuit @ to which 11 is also inputted, transmits the tooth row signal @ to an elliptical orbit 011 shown in Fig. 1.
The signal Cl1l of the weighting coefficient (details will be described later) based on
Calculate by. This processed analog speed signal is converted into a digital signal by an A/D converter.
The film drum (3) is driven by the pulse motor (371Y) via the pulse motor drive circuit
It rotates in the direction of arrow (81) shown in the figure. In other words, the cllC321C (41m block) is the trajectory control circuit that controls the scanning speed of the image scanning means.
The diagram shows the general processing method of this invention! The general system flowchart showing fs'4 is the flowchart and time chart of the subroutine (to) (09) related to tooth row detection and film drum rotation control (hereinafter referred to simply as rotation control) among the subroutines shown in this flowchart. Block diagrams and circuit diagrams are shown in Figures 6 to 9, and these subruples (381ff1
91 is configured to perform parallel processing in order to increase the processing speed #'.The reason why each subroutine is configured in parallel is to reduce the time required to collect dental curvature data and to process the collected data, i.e., automatically. By processing the weighting for creating diversion data and controlling the rotation motor using the machining data in real time, it is possible to obtain finer tooth electric data without increasing the maximum operating frequency of the circuit used. Decide to make it seem possible.

The drawings below show how each routine is connected to the station. Figure 6 ■■,
Fig. 7 ■■ and Fig. 8 ■■ are the ultrasonic transmission/reception control unit that collects dental alignment data, that is, block α31 (toward) in Fig. 4.
This relates to the part (c) and is an embodiment of an ultrasonic probe and a dentition detection circuit provided in one image recording means, which is one of the machine parts of the ninth invention.

As for the control method, the 2s on the self-propelled type and the synchronous type are shown in the figures above.
For simplicity, we will use a self-propelled control system as an example. That action! 132 clear.

FIG. 6 is a diagram showing an example of a self-propelled ultrasonic transmitter/receiver circuit (40), in which a monostable multivibrator f4]1 f4
1'l (431.

OR circuit +441 (451) and a pulse generation circuit consisting of a flip-flop (461) and an integrator (461)
9, capacitor (equipped with a sample hold circuit and an analog switch 15)
521. Figure 7 ■ is a time chart showing the signal waveforms of each part of the circuit (the hook), and the horizontal axis (1
+ indicates time.

It will be connected to the station as shown in Figure 6 (■) above. Now X-ray exposure switch + 1
531 il (t+) II K ON sat'1
．． l & X, m all JN signal (SA)
A trigger signal (SB') unique to the free-running type is outputted from the differential circuit (incorporated) and appears at the output terminal of the OR circuit (44). This is the first signal (SB') of the echo signal (SB) on the time chart, and is not a regular reflection signal of the ultrasonic wave input from the echo terminal (FT), but this free-running circuit (
40) is a pseudo signal for starting the start reflection signal shown in FIG. The analog switch (521) is turned on by this (SB') signal, and the integral output transfer signal (SC) is turned on until (t2).However, at the time (t2) in the initial state, the output signal of the integrator +471 (
SG) is zero and there is no signal to be transferred. Therefore, in this state, the film drum (3) does not rotate, but the time from (Ll) to (t, z) t is several + u
Since the moment is less than a ee e, there is no problem at all when using it. At the end of the above transfer signal (SC) (t2), the integrator signal (SE) is output, and the integrator output (8G)
is set to a constant voltage (el), and triggered by this signal (SG), an ultrasonic probe (not shown) K radiation command signal (SF) is output from the radiation command terminal (RT). SF) signal outputs only one pulse of ultrasound,
At the same time, the OR circuit (45) and flip-flop (46) operate to output an integrator discharge signal (8D) that turns on the analog switch (51). Therefore, the integrator output (SG
) decreases depending on the time constant of the integrator (47) as shown in the figure. As shown in Figure 2, the emitted ultrasonic pulse is reflected and input to the ECO terminal (ET) at the point L4), and only then is the normal reflected signal (SB+) output from the OR circuit (44). and the above reflected signal (SB+) of the integrator output (SG) K corresponding signal (SGl) 'k ''j
7 Full yh - Rotate times N (4Bl (Transfer to 49i, and output the sample and hold device output signal (
It is output as the first signal (SB+) of SH). Since the ultrasound reflected signal (SB+) includes echoes from all parts as shown in Figure 3, only the echoes necessary for detecting the patient's dentition are received as shown in Figure 4. The signal to be discriminated by the signal processing circuit is determined by detecting the reflection time between these signals (in the air, By multiplying the sound wave propagation speed of each body (lip body and dentary bone) by a normalized coefficient, the distance from the radial position on the probe's rotational trajectory, which is known in advance, is detected. And this operation′? By repeating this process, it is possible to continuously detect the unknown dental deposit layer trajectory () IIX of any subject, and as mentioned above, the above detection can be performed in the traveling direction () of the film drum (3). d) (see Figure 1.2), the X-ray beam (XB)
Since this is performed prior to the X-ray imaging, it is possible to detect the predental tomographic trajectory (IIX) in real time during X-ray photography and to control the rotation of the film drum (3) in the arrow (lt1) direction. The reflected signal (SB) is (SB
summer) (SB2)... is input according to the position of the dentary bone, and the center position of each bone (fault trajectory position ff1
) The rotation control signal (SH) changes as follows (SIII) (SB2) depending on the distance (Lh) from the probe to This indicates that control is performed to increase the rotation speed of the film drum (3) for teeth where (Lh) is large, -1, that is, to decrease the rotation speed for teeth that are far away. FIG. 8 is a flowchart showing the signal processing procedure when the above-mentioned self-propelled ultrasonic transmitter/receiver circuit is formed, for example, by a microcomputer. 2 is a configuration of an embodiment of an ultrasonic transmitting/receiving circuit (Circuit) and its time chart.

Furthermore, a flowchart in the case of using a microcomputer will be explained. A synchronizing signal generating circuit (59) with the same symbol - as in Figs. ') occurs as shown in Figure 7■,
The only difference is that triggered by this, an integrator set signal (sg) and further an ultrasonic radiation signal (SF) are output, and other aspects are exactly the same. This can be synchronized with the weighting factor addition routine described later and eliminates the need to collect more dental bone data than is necessary, so the maximum operating frequency of the control circuit can be lower than that of the above-mentioned self-propelled type. can. On the other hand, the resolution of the dentary bone data is lower than that of the self-propelled type,
Sufficient negative and negative data can be obtained by appropriately selecting the frequency of the synchronizing pulse (<sA). Therefore, not only a pulse motor but also an analog ACl or DC servo motor can be used as the film drum driving motor. The flowchart shown in FIG. 8 (■) does not require the reflection signal for starting of the self-propelled type shown in FIG.

Next, the weighting coefficient setting process will be explained with reference to FIG. As explained in Fig. 1, the weighting coefficient is basically configured so that this device always photographs the dental arch (4) having a pseudo-elliptical curve in square projection, and the film drum (31) When continuously rotating (revolving) on an elliptical orbit (3K) similar to a curved curve, the rotation speed of the film drum (3) is not constant over the entire tooth row (4), so the rotation speed of the film drum (3) is It can also be called a correction coefficient that corresponds to fc. In Fig. 1, the film drum (3) moves along its orbit (3K) to (3a) by iiK and has an orbital speed of 7. The speed gradually decreases, reaches the lowest speed near (3a), and then moves in the right direction from (3a).
When rotating, the speed is gradually increased and when it reaches the end point opposite to that shown in Figure 9, the orbital speed of the string is m'v,=. In this way, since the revolution speed (v2) of the film drum (3) differs depending on the photographing position of the dentary bone (4), the rotation speed (vl) of the film drum (3) is changed accordingly. , the weighting coefficient setting circuit shown by the block circle in Fig. 4 processes the above-mentioned dental deposit layer trajectory data. First, the six data (S
H) is (SH+) (SH2) in ■ in Figure 7.
Since each adjacent tooth has a difference and is discontinuous, this is input to the weighting coefficient multiplier as analog data (AH) smoothed by the smoothing circuit shown in FIG.

On the other hand, the number of revolution drive pulses (112) from the revolution motor drive unit of the film drum (3) is counted by the up/down counter, and this is counted by the count output comparison circuit 1.
6), the momentary imaging center position with respect to the front of the dentition (4) is detected. The weighting coefficient (Kl) corresponding to this detected position is applied to the squaring multiplier which is input to the weighting coefficient multiplier. In other words, the data (A ) I) is subjected to the weighting coefficient <SOW@sign calculation and outputted to the A/D converter shown in Fig. 4 above as the data (to) of the film drum rotation speed (v3) according to the position. , the film drum (3) is rotated on its own axis through each of the flow rollers shown in the same figure.

The image recording means, which is one embodiment of the present invention, is used as an X-ray camera, and the film is scanned and the trajectory is determined based on the pre-dental signal detected by ultrasound. This is an explanation of a device in which the drive unit is driven by a pulse motor via a control circuit.
The configuration of the overcontrol circuit is not limited to what is shown or explained; for example, instead of the integrating circuit in Figure 6, a preset type counter may be used, and the preset count number is shown in Figure 7. By causing the counter to count up or down using pulses with high accuracy during the integrator discharge period of T(SD) shown in FIG. Also, in Figure 9, taking advantage of the fact that the film drum orbit ((3K) in Figure 1) is line symmetrical with respect to the center of the orbit, UP ti is used as a down only counter instead of an up/down counter. Furthermore, the weighting coefficient circuit can also be configured by an analog signal circuit using an integrator.

In this way, by appropriately connecting a D/A converter in the circuit, it is possible to determine whether the control signal is an analog value or a digital value! In addition to smoothing the tooth electric detection signal, this means that the film drum rotation drive motor can be a digital pulse motor, and analog AC or DC motors can be used. This shows that it can be used in either case.

Next, as a second embodiment of this invention, 1 image recording means 4
Instead of using an X-ray film, the system converts the transmitted dental arch X-rays into visible light and then stores it in a digital image memory, and the image can be displayed on a CRT monitor simultaneously or at any time. I will explain about the equipped GT. Figure 10 is the digital image memory mentioned above? 7110
This is a three-dimensional schematic diagram showing the configuration.
) is a memory corresponding to the X-ray film surface, and (C) is a gray scale memory for expressing the photographic immersion level appearing on the X-ray film. Now, for example, this memory ff1l is a X b = 5 J 2 X ] 01
2, c = 64, the rise of the X-ray film used for panoramic photography (150x
Resolution o2 at 300mm)! +iJ, which is on the same level as 64 gradations, and is fully usable for practical use. Next, in Figure 11.

A block diagram of the control circuit ff21 for storing the dental electrotomogram in the image memo U ff1l will be shown and its operation will be explained.

Based on the output data 1 of the above-mentioned patient-specific dentition tomographic trajectory data output circuit No. 3), that is, the pre-dentition data to which the weighting coefficient LKl has been added, fC is proportional to that data.
Sequence (Pv) f A Sequence occurrence wXff3) K
and generate it. The frequency of this pulse train (Pv) is equivalent to the rotation speed (v3) of the film drum (3) described above. The column address generation circuit of the memory of ff41 is a generation circuit of an address signal (Sj) for controlling the (jl Y) of the memory number (M i j ) shown in FIG. 10, and is composed of a counter.17 Therefore, since the counter output changes in proportion to the pulse frequency output from the pulse train generator circuit (supply), the image memory ff11, which is operated by this output, This function is equivalent to rotating the film (2). Furthermore, the memory row address generation circuit σ5
H-t, the vertical synchronization signal of the imaging unit control circuit Is ff61 is the basic signal and 1. The memory number (Mij) shown in Figure 10
Address signal (Si) for controlling (il) 'F
Specific power. In this way, the image memory 61) stores the output visible light image of the X-ray image visible light converter (equipment) from the image tube or the tomographic plane g# signaled by the imaging unit (781) such as a CCD. This is the same principle as recording the tomographic image on the film described above.In the figure, t79j is a circuit that amplifies the image signal, and (a) is a circuit that amplifies the analog video signal. The dental fossa tomographic image recorded in the image memo IJ (7) 1 can normally be observed in real time on a CRT monitor controlled by a CRT control circuit (81). This is a convenient point compared to X-ray film.

Since the operator's observation is performed immediately, imaging can be performed with the diagnostic accuracy required by the operator. Also, the fault g#woflo 1
．． Record and save by transferring to a disc or hard copy. This method has the advantage that it is relatively easy to perform both processing of X-ray images, so more information can be obtained from the original image.

Next, FIG. 12 shows a third embodiment of the present invention and [7
The analog image memory used as an image recording means is used as a means of image recording.
The analog image memory control circuit (c) differs from the digital image memory circuit fi2+ in that the memory vil is
λ is used as a video recorder such as a video tape recorder or a video disc.
The circuitry for storing the IIi image in the video recorder (a) is all operated using analog signals, so the circuit configuration is quite simple. Based on the signal output from the dental curvature data output circuit (63).

The scanning control circuit generates a signal (Sv) that controls the rotation of the drive motor, ie, the image scanning speed, of, for example, the video recorder (a), thereby rotating the tape or dinuk of the video recorder (a). This rotational speed is equivalent to the speed at which the film drum (3) of the first embodiment rotates.
6) outputs a vertical synchronizing signal to the video recorder (a). In this way, the tomographic image is recorded on the video recorder 1B6). The image reproduction is the same as described above.

The above are some embodiments of this invention.

It goes without saying that the present invention is not limited to the illustrations and descriptions; for example, the film drum of the first embodiment is not limited to the two-arc shape, but can be similarly applied to flat cassettes.

Since this invention is constructed as described above, it is completely different from conventional dental equipment. 1liXf+! This solves the drawbacks and disadvantages of imaging equipment and detects the dental curvature of any patient in real time during X-ray imaging by using ultrasound.

Since the trajectory can be controlled based on this detection, it is possible to perform Xl# imaging using the most accurate tomographic trajectory, which is the most basic method in m-pan tomography.

Good quality X111i! The ability to easily obtain information, especially the ability to obtain accurate tomographic trajectories through ultrasonic detection, means that, for example, when using a digital image memory, the capacity of the tomographic data storage system can be reduced. . In this way, the present invention completely eliminates the operator's trouble in inspecting the dental cavity and the patient's pain during imaging, and also provides easy-to-operate, useful, and accurate X-ray information9. It was possible to provide a convenient device ii with excellent diagnostic effect,

[Brief explanation of drawings]

Figure 1 is a schematic (plan) diagram showing the configuration of the dental full-jaw X-tight imaging device of the first smiling example of this invention, Figure 2
Front view showing the ultrasonic probe attached to the film drum of m, vf! I■ is a side view of the subject's head showing the positional relationship with the above-mentioned probe during positioning, Fig. 3 is a time cheat of the transmission and reception signals of the above-mentioned ultrasound probe, and Fig. 4 is the circuit of the above-mentioned device. Figure 5 is a general system flowchart of the above device; Figure 6 (■) is a self-propelled ultrasonic transmission/reception control circuit diagram of an embodiment of the present invention; Figure 0 (■) is a synchronous ultrasonic transmission/reception control circuit diagram; Figure ■ is a time chart of signals of each part of the above self-running control circuit, Figure ■ is a time chart of signals of each part of the above synchronous control circuit, Figure 8 is a flowchart of the above self-running control circuit, and Figure ■ is a time chart of signals of each part of the above-mentioned synchronous control circuit. FIG. 9 is a block diagram of the weighting coefficient circuit in the orbit control of the present invention, and FIG. 10 shows the configuration of the digital image memory of the second embodiment of the device of the present invention. FIG. 12 is a block diagram of the digital image memory control circuit described above, and FIG. 12 is a block diagram of an analog image memory control circuit according to a third embodiment of the present invention. 1... X-ray source xB... Radiation beam 2... X@film as an example of image recording means 3... Film drum as image receiving and scanning means 4... Teeth row 5... Arm 6, 6R, 7, 8, 9 -- Arm rotation drive means 11.
... Dental curvature fault trajectory 11X...Dental curvature fault trajectory 13 unique to the examinee...Ultrasonic probes 25, 28, 40, 56... Dental curvature detection circuit 30, 3
2, 34, 36--Trajectory control circuit 37...Pulse motor 71--Digital image memory 77...Image conversion section 78...Imaging section 80...AD
Conversion section 86... Analog image memory patent applicant Asahi Roentgen Industries Co., Ltd.

Claims (1)

[Scope of Claims] 1. An X-ray source suspended at one end of an arm, and an X-ray source suspended at the other end of the arm in a predetermined relative relationship position between the X-ray source and the dental cavity of the subject. , and the image recording means for capturing the dental electrotransmission X-ray image, and the predetermined relative relationship is maintained.XI! i! arm rotation driving means for rotating the arm so as to always squarely project the radiation beam of the source onto the tooth array; #cft is equipped with an image receiving and scanning means that continuously scans blue transmitted X-ray images, and is configured to take a panoramic image of the whole jaw of the subject, and the image recording means is equipped with an ultrasonic probe. and a dental fossa detection circuit that controls this probe and detects the orbit of the dental deposit layer specific to the subject in real time when photographing, and also controls the scanning speed of the image receiving and scanning means. is detected by the detection circuit,
A complete dental X-ray imaging apparatus comprising: an axial path control circuit that performs control based on a dental curvature signal to enable scanning of the orbital tomographic plane; 2 Image recording means'? The image receiving and scanning means for this X-ray film is based on the output signal of the orbit control circuit? The dental full jaw X-ray imaging Mii, 3, Ii image recording means according to claim 1, which is formed by a pulse motor driven by a pulse motor, is an X-ray film, and the image receiving and scanning means for this X-ray film is a trajectory control circuit. 2. A dental full-mouth X-ray imaging device according to claim 1, which comprises a servo motor driven by an output signal. 4. The image recording means includes an image converting unit that converts the fi-row transmitted X-ray g# into a visible light image, an imaging unit that outputs this visible light image as an image signal, and an AD that digitizes this image signal.
A dental full-mouth X-ray photographing apparatus according to claim 1, comprising a converter and a digital image memory for scanning and storing the digital signal by a trajectory control circuit of an image receiving and scanning means; 5. an image recording means; an image converting section that converts a dental fossa transmission X-ray image into a visible light image; an imaging section that outputs this visible light image as an image signal; and this image signal is scanned and stored by a trajectory control circuit of an image receiving and scanning means. A dental full-mouth X-ray imaging device according to claim 1, comprising an analog image memory.