JPH0419856B2 - - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a full-mouth X-ray imaging device for dental treatment that can take panoramic photographs of not only the dentition area but also the oral cavity function and the facial area including the upper and lower jaws.

Most of the documents, patents, or utility models that describe the method of controlling the dentition tomography trajectory of the dental full-mouth X-ray imaging device (hereinafter referred to as the panoramic device) that has been published in the public domain are This paper discusses only means for moving the X-ray film image-receiving surface along the known pseudo-elliptical trajectory, assuming that the tomographic trajectory is known. Therefore, if there are parts of a subject's unique tomographic trajectory that differ from the known standard trajectory, the different parts may be blurred in the dentition panoramic photograph, making it difficult to obtain accurate X-ray information. There is a problem in that the diagnostic accuracy is lowered. 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-mentioned control. In other words, the trajectory detection method unique to the examinee is to have the examinee chew on a matrix plate that can electrically detect the dentition, or to use something like plaster or wax sheet to detect the dentition. The method is to take copies of the data and obtain data on the dentition curve from them. Conventional devices that involve preprocessing operations for data collection have the disadvantage that they not only complicate the operator's work and require time and effort, but also cause considerable pain to the subject. Furthermore, when the various dentition 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 when performing full-jaw photography using a conventional panoramic device,
This method solves the drawbacks and problems of pretreatment operations using dentition testing instruments that have been used to improve diagnostic accuracy. In other words, 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 patient's individual dentition tomographic trajectory in real time are used to create an image. The recording means is provided with an image receiving trajectory control circuit which controls the image receiving scanning speed in real time based on the output signal of the detection circuit, in other words, the tomographic trajectory signal, and makes it possible to image a tomographic plane of the dentition unique to the subject. The present invention relates to an apparatus characterized in that it is provided in a 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 discomfort for the patient, but also allows the patient's individual dentary fault trajectory to be determined with great accuracy. The objective is to provide a convenient device that can detect the trajectory and at the same time take sharp images of 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 construction of a dental full-mouth X-ray photographing apparatus in which an X-ray film is used as an image recording means as a first embodiment of the present invention. An X-ray tube 1 as an X-ray source and an X-ray film 2 as an image recording means are attached to the film drum 3 as an image receiving and scanning means that scans (rotates in this example) in the direction of arrow a. The teeth of the arms 5 are suspended at both ends of the arms 5, facing each other with the teeth 4 interposed therebetween. Arm 5
A planetary friction wheel 6 is fixed on the upper part of the planetary friction wheel 6, and the central axis 7 of this wheel 6 is rotated through an arm 6R about a shaft 9 provided at the center of a fixed solar friction wheel 8 having a friction transmission part on the inner surface. It is supported so that it can rotate freely and so that the inscribed contact of the roller wheel 6 with the friction ring 8 is not cut off. In this mechanism, when the central shaft 7 is rotated in the direction of arrow b, the rolling wheels 6 are rotated by the friction wheels 8
It revolves around itself while rotating in the direction of arrow c along the inner surface of
Move to position 6a. Therefore, the arm 5 fixed to the wheel 6 is at the position 5a shown by the dotted line,
The X-ray tube 1 and film drum 3 suspended on the arm 5 take positions 1a and 3a, respectively. As the rotation progresses further, the wheel 6 becomes 6b and the arm 5 becomes 5b.
come to the position. In this rotation, the locus 11 of the movement of the fixed point 10 passing over the tooth row 4 of the subject on the arm 5 is a pseudo-elliptical continuous curve that closely resembles the tooth row 4 (dental row layer) as shown in the figure. orbit),
A rolling wheel 6 and a friction ring 8 are configured. For this purpose, the film drum 3 suspended from one end of the arm 5 continuously moves on a track 3K parallel to the tooth row 4, thereby reaching a fixed point 10 of the arm.
In other words, the relative relationship between the distance La of the focal point 1X of the X-ray source with respect to the tooth row fault trajectory 11 and the distance Lb of the film 2 with respect to the fault trajectory 11 is always maintained constant, and The X-ray radiation beam X _B , which coincides with the central axis of the arm 5 through the slit, is on the normal line passing through the center of curvature of the above-mentioned tomographic trajectory 11, that is, it continuously projects the dentition 4 in a tetragonal manner. It rotates.
The above structure and operation are the same as those of the conventional device, and the main part of the present invention is an ultrasonic probe provided at a position preceding the movement of the X-ray entrance slit 12 in the direction of arrow d due to the aforementioned rotation of the film drum 3. 13, a dentition detection circuit that controls transmission and reception of ultrasonic waves of this probe 13 and detects the dentition fault trajectory 11X unique to the subject immediately before imaging, and this detection signal. This orbit control circuit controls the rotational (scanning) speed of the film 2 in the direction of arrow a based on the above-described trajectory control circuit to photograph the individual tomographic plane. These will be explained step by step. Figure 2A shows the X-ray source 1 of the film drum 3.
Figure B is a side view of the subject's head 14 showing the vertical positional relationship between the film drum 3 and the ultrasound probe 13 during positioning of the subject. . In Fig. A, a slit 12 is formed in the center of the front cover 16 of the film drum 3 suspended by the suspension arm 15 that engages with one end of the arm 5. Probe guide grooves 17 provided close to each other and parallel to each other are formed in a structure that prevents X-rays from entering the film 2, and support the probe 13 so as to be movable up and down. The ultrasonic probe 13 includes a piezoelectric vibrator made of lead zirconate titanate, which has a diameter of about 8 to 10 mm, and is of a circular plate type or a concave convergence type, and a piece of rubber, for example, that absorbs unnecessary ultrasonic waves emitted from the back side of the vibrator. The system consists of an absorber and a substrate member that supports the transducer and the absorber, and the frequency of the emitted ultrasound is determined by the thickness of the transducer, for example, 2MHz, and the thickness of the ultrasound beam is determined by the thickness of the transducer. The length is determined by the diameter mentioned above.

Next, the relationship between the positioning operation of the subject's head 14 and the position adjustment of the probe 13 will be described with reference to FIG. The positioning operation is carried out by inserting two parallel light beams 18 and 19 from the projector (not shown) provided in the device, the upper beam 19 into the lower rim of the orbit 20 and into the ear holes inserted into both external auditory canals as shown in the figure. The chin rest and head rest (not shown) are adjusted to match the eye-ear plane 22 connecting the upper edge 21 (not shown). By this adjustment, the tooth row 4 of the head 14 is correctly positioned horizontally, and at the same time, the midline is determined by a mirror (not shown), and the positioning is completed. At this time, the lower beam 1 is made parallel to the beam 19 and whose interval W can be freely adjusted.
8 is aimed at the position of the dentition 4 of the subject, the beam 18 is irradiated orthogonally to the probe guide groove 17 of the film drum 3 as shown in Figure A, and the beam 18 is By aligning the centers of the tentacles 13, the positioning of the subject's dentition 4 for emitting ultrasonic waves is completed. When an ultrasonic pulse of, for example, 2 MHz is emitted from the ultrasonic probe 13 that is positioned in this manner, it will be emitted from the interface between two substances with different acoustic impedances (density x sound speed), such as air and skin. Reflected waves (echoes) are returned due to impedance mismatch. FIG. 3 is a time chart of the ultrasonic transmission and reception signals, where the vertical axis V shows the magnitude of the signal, and the horizontal axis t shows the passage of time. Now, if A is the radiation signal, B is the echo at the interface between the probe and the air, C is the echo at the subject's skin surface, D is the echo at the outer surface of the tooth row,
E is an echo from the inner surface of the dentition, and F is an echo from the jawbone on the opposite side. These transmitted and received waveforms are based on a pulse reflection method generally called A mode, and if the positions of the echoes D and E are known, the position of the unknown tomographic trajectory 11X located in the center can be detected. FIG. 4 shows a basic circuit block diagram of the present invention for the embodiment device explained in FIG. 1 above. Ultrasonic transmission/reception control circuit 25
emits a radiation signal 26 to the probe 13, and
It controls the operation of a circuit 28 that processes the reflected signal 27 received by the probe 13. The blocks 25 and 28 form the dentition detection circuit, and the output signal 2
9 is the dentition signal. A film drum rotational speed setting circuit 32 to which this signal 29 and an output signal 31 of a weighting factor setting circuit 30 are input together is configured to convert the tooth row signal 29 into a weighting factor (details) based on the elliptical trajectory 11 shown in FIG. will be described later). This processed analog speed signal 33 is converted into a digital signal 35 by an A/D converter 34, and the pulse motor drive circuit 3
6, the pulse motor 37 is driven to rotate the film drum 3 in the direction of arrow a shown in FIG. That is, the above 30, 32, 34,
Block 36 is a trajectory control circuit that controls the scanning speed of the image scanning means. FIG. 5 is a general system flowchart showing the general processing procedure of the present invention, and is shown in this flowchart. Flowcharts, time charts, block diagrams, and circuit diagrams of subroutines 38 and 39 related to tooth row detection and film drum rotation control (hereinafter simply referred to as rotation control) are shown in sections 6 to 6.
It is shown in FIG. And these subroutine 3
8 and 39 are configured to allow parallel processing to increase processing speed. The parallel processing configuration of each subroutine was designed to reduce the time required to collect tooth row data, process the collected data, that is, weight processing to create data for rotation, and control the rotation motor using processed data in real time. This is to make it possible to obtain finer dentition data without increasing the maximum operating frequency of the circuit used.

Each routine will be explained below with reference to the drawings. 6th
Figures A and B, Figures 7A and B, and Figures 8A and B relate to the ultrasonic transmission control section for collecting dentition data, that is, blocks 13, 25, and 28 in Figure 4, and are related to the invention. It is one of the main parts of This is an example of an ultrasonic probe and a dentition detection circuit provided in an image recording means. Two types of control methods, a self-propelled type and a synchronous type, are shown in A and B of each of the above figures.
For the sake of simplicity, the operation will now be explained using a self-propelled control system as an example. FIG. 6A is a diagram showing an example of the self-propelled ultrasonic transmitter/receiver circuit 40, in which monostable multivibrators 41, 42, 43, OR circuit 4
4, 45 and a flip-flop 46; an integrator 47; a sample-and-hold circuit consisting of a capacitor 48 and an amplifier 49; and analog switches 50, 51, and 52. FIG. 7A is a time chart showing signal waveforms at various parts of the circuit 40, and the horizontal axis t indicates time, which will be explained in conjunction with FIG. 6A.
When the X-ray exposure switch 53 is turned on at time _t1 , the X-ray exposure signal SA is output and a trigger signal SB' unique to the free-running type appears from the differentiating circuit 54 at the output terminal of the OR circuit 44. This is the first signal SB' of the echo signal SB of the time chart, and is not a regular reflected signal of the ultrasonic wave input from the echo terminal ET, but a pseudo signal for starting this free-running circuit 40. This is the starting reflected signal shown in .
The analog switch 52 is activated by this SB' signal.
It is turned ON, and the integral output transfer signal SC remains ON until _t2 . However, at time _t2 in the initial state, the output signal SG of the integrator 47 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 t ₁ to t ₂ is several milliseconds.
Since the moment is as follows, there is no practical problem at all. At the end of the transfer signal SC, at _t2 , an integrator set signal SE is output, and the integrator output SG is set to a constant voltage e, and triggered by this signal SG, an ultrasonic probe (not shown) is Radiation command signal SF is output from radiation command terminal RT. This SF signal causes only one pulse of ultrasonic waves to be output, and at the same time, the OR circuit 45 and flip-flop 46 operate to output an integrator discharge signal SD that turns on the analog switch 51. Therefore, the integrator output SG is integrator 4
It decreases as shown in the figure with a time constant of 7. The emitted ultrasonic pulse is reflected as shown in Fig. 2 and is input to the echo terminal ET at time _t4 , and only then is the normal reflected signal _SB1 output from the OR circuit 44 and the integrator output SG. The signal SG ₁ corresponding to the reflected signal SB ₁ of
9, and output from the output terminal of the ultrasonic transmitter/receiver circuit 40, that is, the rotation control signal terminal CT, as the first signal _SH1 of the sample-and-hold device output signal SH. Since the ultrasonic reflected signal SB ₁ includes echoes from all parts as shown in Fig. 3, only the echoes necessary for detecting the dental arch of the subject are included in the ultrasonic reception signal shown in Fig. 4. Discrimination is made by the processing circuit 28. The signals to be discriminated are B, C, D, and E in Fig. 3, and the reflection time between these signals is detected, and the region through which the signal passed during that reflection time (the air, the flesh of the lips, and the dentary bone) is determined. By multiplying each sound wave velocity by a normalized coefficient, the distance from the predetermined radiation position on the probe's rotational trajectory is detected. By repeating this process, it is possible to continuously detect the unknown dentition cross section trajectory 11X of any subject. Furthermore, as mentioned above, the above detection is performed in advance of the X-ray beam XB in the traveling direction d of the film drum 3 (see Figures 1 and 2), so that the dentition layer can be detected in real time during X-ray photography. It is possible to detect the trajectory 11X and control the rotation of the film drum 3 in the direction of arrow a. Returning to FIG. 7A, the reflected signals SB are SB ₁ , SB ₂ ...
is input according to the position of the dentary bone, and SH ₁ , SH ₂ , etc. are rotated according to the distance Lb from the probe to the center position (fault trajectory position) of each bone. The control signal SH changes, e.g.
Film drum 3 for close teeth with small Lb
This shows that control is performed to increase the rotation speed of the tooth, and to decrease the rotation speed for teeth with large Lb, that is, teeth that are far away. FIG. 8A is a flowchart showing a signal processing procedure when the self-propelled ultrasonic transmitting/receiving circuit is formed by, for example, a microcomputer. Next, FIG. 6B, FIG. 7B, and FIG. 8B show an example circuit 56 of the synchronous ultrasonic transmitter/receiver circuit.
The configuration, its time chart, and a flow chart when using a microcomputer will be explained. Those with the same symbols as those in FIGS. 6 to 8A will not be described in detail.Different from the above-mentioned self-running circuit 40, they include a synchronizing signal generating circuit 59 consisting of a multivibrator 57 and a flip-flop 58, and an X-ray exposure switch 53. When it is turned on and the X-ray exposure signal SA is generated, a synchronous pulse signal SA' is generated as shown in Fig. 7B, and triggered by this, the integrator set signal is
The only difference is that SE and 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.
Since it is possible to avoid collecting more dentition data than necessary, the maximum operating frequency of the control circuit can be lower than that of the above-mentioned free-running type. On the other hand, the resolution of the tooth row data is lower than that of the self-propelled type, but if the frequency of the pulse SA' is appropriately selected, data of sufficiently high quality can be obtained. Therefore, not only a pulse motor but also an analog AC or DC servo motor can be used as the film drum drive motor. In the flowchart of Figure 8B, the self-propelled starting reflection signal of Figure A is not required.
This shows that a synchronization signal is used instead.

Next, the weighting coefficient setting circuit 30 will be explained with reference to FIG. As explained in FIG. 1, the weighting coefficient is such that this device is basically configured to always image the pseudo-elliptic curved tooth row 4 in square projection.
When the film drum 3 continuously rotates (revolutions) on an elliptical orbit 3K similar to the tooth row curve, the revolution speed is not constant over the entire tooth row 4, so the rotation speed of the film drum 3 is This can also be called a correction coefficient that corresponds to this. For example, in FIG. 1, the film drum 3 has its orbit 3
When moving K to position 3a, its orbital speed is gradually lowered, reaching the lowest speed near 3a,
When moving further to the right from 3a, the speed is gradually increased, and when it reaches the end point on the opposite side of the figure, it resumes its original revolution speed. In this way, the revolution speed of the film drum 3 is determined by the photographing position of the tooth row 4.
Since v ₂ is different, the rotational speed v ₁ of the film drum 3 is changed accordingly.In other words, the weighting coefficient setting shown in block 30 of FIG. It is a circuit. First, the data obtained in Figures 6, 7, and 8
SH has a difference between adjacent teeth as shown in FIGS. 7A and 7B, SH ₁ , SH _{2 .} . . and is discontinuous, so this is smoothed by the smoothing circuit 62 in FIG. The data is input to the weighting coefficient multiplier 63 as data A _H. On the other hand, the number n ₂ of revolution drive pulses from the revolution motor drive unit 64 of the film drum 3 is counted by an up-down counter 65, and this is counted by a count output comparison circuit 66 to determine the instantaneous shooting center position with respect to the tooth row 4. To detect. The weighting coefficient K corresponding to this detected position is taken out from the storage memory 68 via the address decoder 67 and inputted to the weighting coefficient multiplier 63 as analog data S _K by the D/A converter 69. In other words, the multiplier 63 multiplies the smoothed dentition data A _H corresponding to the film drum rotation speed v ₁ by a weighting coefficient A _K , and outputs it as data 33 of the film drum revolution speed v ₃ corresponding to the position. The fourth A/D shown in
The signal is outputted to the converter 34, and the film drum 3 is then rotated through each block shown in the figure.

The above is an embodiment of the present invention, in which the image recording means is an X-ray film, and the film drum that scans the film is controlled by a pulse motor via an orbit control circuit based on a tooth alignment signal detected by ultrasonic waves. Although this is a description of the driving device, the configurations of the dentition detection circuit and the trajectory control circuit are not limited to those illustrated or described. For example, 6th A, B
In the figure, a preset-type counter is used instead of an integrating circuit, and the preset count number is set to 7A and B.
An integrator output signal equivalent to (SG) in the figure can be obtained by causing the counter to count up or down using pulses with high accuracy during the integrator discharge period (SD) shown in the figure. Figure 9 also shows the orbit of the film drum (3 in Figure 1).
Taking advantage of the fact that K) is line symmetrical with respect to the center of the trajectory, it is possible to use only an up or down counter instead of an up-down counter, or even by using an analog signal circuit using an integrator. A weighting coefficient circuit can be constructed. In this way, by appropriately connecting an A/D or A/D converter in the circuit, it is possible to control whether the control signal is an analog value or not.
The control circuit can be constructed regardless of whether the value is a digital value, and this means that in addition to smoothing the tooth row detection signal, the film drum rotation drive motor can be controlled by a digital pulse motor or an analog AC This indicates that it can be used with either a DC motor or a DC motor.

Next, as a second embodiment of the present invention, the image recording means does not use an X-ray film, but instead uses a method in which the transmitted X-ray image of the dental arch is converted into a visible light image and then stored in a digital image memory. A device in which images are displayed on a CRT monitor screen simultaneously or at any time will be described. FIG. 10 is a three-dimensional schematic diagram showing the configuration of the digital image memory 71. In the figure, (a x b) are memories corresponding to the X-ray film surface, and c is the memory corresponding to the photographic density appearing on the X-ray film. This is a grayscale memory for expression. For example, if this memory 71 is composed of a x b = 512 x 1012, c = 64, the x
The resolution is 0.29 mm ^-2 and is equivalent to 64 gradations in the line film size (150 x 300 mm), which is sufficient for practical use. Next, FIG. 11 shows a block diagram of a control circuit 72 for storing a dentition tomogram in the image memory 71, and its operation will be explained.
Based on the output data of the above-mentioned patient-specific dentition fault trajectory data output circuit 63, that is, the dentition data to which the weighting coefficient K has been added, a pulse train Pv proportional to the data is generated in the pulse train generation circuit 73. . The frequency of this pulse train Pv is equivalent to the rotation speed v ₃ of the film drum 3 mentioned above. 74
The column address generation circuit of the memory 1 is a generation circuit of an address signal Sj for controlling j of memory number Mij shown in FIG. 10, and is constituted by a counter. Therefore, since the counter output changes in proportion to the pulse frequency output from the pulse train generating circuit 73, the image memory 71, which is operated based on this output, is able to control the X-ray film 2 set on the film drum 3. The function is equivalent to rotating and moving. Furthermore, the memory row address generation circuit 75
outputs an address signal Si for controlling i of the memory number Mij shown in FIG. 10 using the vertical synchronization signal of the imaging unit control circuit 76 as a basic signal. In this way, the image memory 71 converts the output visible light image of the X-ray image/visible light conversion unit 77, which is an image tube, into a signal by the imaging unit 78, such as an image pickup tube or CCD, and stores the tomographic image in the memory. This is the same principle as recording tomographic images on film as described above. In the figure, 79 is a circuit for amplifying the image signal, and 80 is a converter for digitizing the analog video signal. This image memory 71
Dental arch tomograms recorded in are usually recorded in real time.
CRT monitor 8 controlled by CRT control circuit 81
It can be observed on two sides. This point is more convenient than X-ray film, and since the operator can observe immediately, imaging can be performed with the diagnostic accuracy required by the operator. In addition, the tomographic images are transferred to a floppy disk or hard copy for storage.
This method has the advantage that image processing of X-ray images can be performed relatively easily, and more information can be obtained from the original image.

Next, an apparatus using an analog image memory as an image recording means as a third embodiment of the present invention will be explained with reference to FIG. The analog image memory control circuit 8 in the figure with the same symbol as in FIG. 11 will not be explained.
5 is different from the digital image memory circuit 72 described above in that the memory 86 is a video recorder such as a video tape recorder or a video disk, and the circuit for storing images in the video recorder 86 is all analog signals. The circuit configuration is quite simple since it is easy to operate. Based on the signal output from the dentition data output circuit 63, the scanning control circuit 87 generates a signal Sv for controlling the rotation of the drive motor of the video recorder 86, that is, the image scanning speed;
This causes the disk of the video recorder 86 to rotate. This rotational speed is equivalent to the speed at which the film drum 3 of the first embodiment is rotated. Further, a vertical synchronization signal is output from the imaging unit control circuit 76 to the video recorder 86. In this way, a tomographic image is recorded on the video recorder 86. 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 can be applied not only to an arc-shaped film drum but also to a flat-plate cassette.

This invention is constructed as described above, and thus solves the drawbacks and problems of conventional dental full-mouth X-ray imaging devices, and can examine the dentition of any patient by using ultrasound. Real-time detection during X-ray photography,
Since the trajectory can be controlled based on the detection, it is possible to perform X-ray imaging using an accurate tomographic trajectory, which is the basis of dentition tomography, and it is possible to easily obtain high-quality X-ray information.
In particular, the fact that accurate tomographic trajectories can be obtained by ultrasonic detection means that, for example, when a digital image memory is used, the capacity of the tomographic data storage memory can be reduced. In this way, this invention completely eliminates the troublesomeness of the operator's detection of the dental arches and the patient's pain during imaging, and also makes it possible to obtain accurate X-ray information that is easy to operate, useful, and improves diagnostic effectiveness. This provides an excellent and convenient device.

[Brief explanation of drawings]

1 is a schematic (plan) view showing the configuration of a dental full-mouth X-ray imaging device according to a first embodiment of the present invention; FIG.
Figure A is a front view showing the ultrasonic probe attached to the film drum of the above device, Figure B is a side view of the subject's head showing the positional relationship with the probe during positioning, and Figure 3 is 4 is a circuit block diagram of the above device, FIG. 5 is a general system flowchart of the above device, and FIG. 6A is a self-propelled type according to an embodiment of the present invention. FIG. 7A is a diagram of the ultrasonic transmission/reception control circuit; Figure B is a diagram of the synchronous ultrasonic transmission/reception control circuit; FIG. Signal time chart, No. 8
Figure A is a flowchart of the above-mentioned self-running control circuit, Figure B is a flowchart of the above-mentioned synchronous control circuit,
Figure 10 is a block diagram of a weighting coefficient circuit in orbit control of the present invention, Figure 10 is a schematic (stereoscopic) diagram showing the configuration of the digital image memory of the second embodiment of the invention, and Figure 11 is the digital image memory described above. Block Diagram of Control Circuit FIG. 12 is a block diagram of the analog image memory control circuit of the third embodiment of the present invention. DESCRIPTION OF SYMBOLS 1... X-ray source, B... Radiation beam, 2... X-ray 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 row fault orbit, 1
1X...Subject's unique dentition fault trajectory, 13...
Ultrasonic probe, 25, 28, 40, 56...dental row detection circuit, 30, 32, 34, 36...orbit control circuit, 37...pulse motor, 71...digital image memory, 77... Image converter, 78...imaging unit, 80...AD converter, 86...analog image memory.

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 this arm in a predetermined relative relationship position with the subject's dentition, and
an image recording means for capturing an X-ray image transmitted through the dentition;
The apparatus comprises: an arm rotation drive means for rotating the arm; and an image reception scanning means for continuously scanning a dentition transmission X-ray image on an image reception surface of the image storage means in response to the rotation of the arm; In a device configured to take panoramic images of the examiner's whole jaw X-ray information, the image recording means includes an ultrasound probe, and this probe is controlled to record echoes of the inner and outer surfaces of the dental arch. A dentition detection circuit is provided for determining the center position of the dentition and detecting the dentition ridge tomographic trajectory unique to the subject in real time during imaging, and the image receiving scanning means is provided with a scanning speed detected by the detection circuit. A dental full-mouth X-ray imaging device, characterized in that it is provided with a trajectory control circuit that performs control based on a dentition signal and enables the trajectory tomography. 2. The dental full-mouth X according to claim 1, wherein the image recording means is an X-ray film, and the image receiving and scanning means for the X-ray film is a pulse motor driven by the output signal of the orbit control circuit. Ray imaging device. 3. The dental full-mouth X according to claim 1, wherein the image recording means is an X-ray film, and the image receiving and scanning means for the X-ray film is a servo motor driven by an output signal from an orbit control circuit. Ray imaging device. 4. The image recording means includes an image converting section that converts a dental ridge transmission X-ray image into a visible light image, an imaging section that outputs this visible light image as an image signal, and an A/D conversion that digitizes this image signal. 2. A dental full-mouth X-ray photographing apparatus according to claim 1, comprising a digital image memory for scanning and storing this digital signal by a trajectory control circuit of an image receiving and scanning means. 5. The image recording means converts the dentition transmission X-ray image into a visible light image, the imaging section outputs this visible light image as an image signal, and the image signal is sent to the trajectory control circuit of the image receiving and scanning means. A dental full-mouth X-ray imaging device according to claim 1, comprising an analog image memory for scanning and storing images.