JP5639521B2 - Control device, control method, and control program for dental optical coherence tomographic image generation apparatus - Google Patents

Description

  The present invention relates to a dental optical coherence tomographic image generation device, and more particularly to a control device, a control method, and a control program for a dental optical coherence tomographic image generation device.

  2. Description of the Related Art Conventionally, an optical coherence tomographic image generation apparatus (Optical Coherence Tomography: hereinafter referred to as an OCT apparatus) is applied in ophthalmic medicine such as tomographic measurement of an eyeball cornea or a retina in the field of a living body. OCT is a method that enables non-invasive and non-contact diagnosis by irradiating a living tissue with light. Diagnostic methods other than OCT include CT (Computed Tomography) with a resolution of 200 microns or less, MRI (Magnetic Resonance Imaging) with a resolution of 800 microns or less, and PET (Positron Emission Tomography) with a resolution of 1000 microns or less. Can achieve a resolution of several to several tens of microns, which is much better than these, and can display high-definition images with high resolution. This OCT method is broadly divided into TD (Time Domain) -OCT and FD (Frequency Domain) -OCT. The latter FD-OCT includes SD (Spectrum Domain) -OCT and SS (Swept Source) -OCT. It is known that it is classified into

For example, SS-OCT is a method of specifying an optical path length by using a laser light source capable of continuously sweeping a wavelength (wave number), subjecting spectrum information acquired by a detector to FFT (Fast Fourier Transform) processing. SS-OCT has features such as higher resolution and measurement in real time without exposure compared to, for example, X-ray imaging apparatuses and CT apparatuses that are widely used in dentistry.
In addition, the TD-OCT described above has been tried for dental use, but since SS-OCT can acquire data with higher sensitivity and higher speed than TD-OCT, motion artifact (ghost due to body movement) It is characterized by being strong.

The OCT apparatus obtains one tomographic image as a direction perpendicular to the laser irradiation direction (vertical direction or depth direction of the subject) to the front of the subject, and the width direction (left and right direction of the subject) and depth. Since two-dimensional mechanical scanning in the direction (front-rear direction of the subject) is necessary, it takes time for imaging and consequently diagnosis.
In an OCT apparatus for ophthalmology, a technique for acquiring a schematic image of a subject before capturing a detailed image used for diagnosis is known (see Patent Document 1).
The imaging apparatus described in Patent Literature 1 includes a cross-sectional image acquisition unit realized by an OCT apparatus, and a front image acquisition unit realized by a fundus camera for acquiring a front image, an SLO (Scanning Laser Ophthalmoscope), and the like. The front image acquisition unit acquires a schematic image of the subject. This imaging apparatus displays a front image (fundus surface image), which is a schematic image of a subject, and a cross-sectional image (tomographic image) side by side on a GUI (Graphical User Interface) screen. Then, the photographing position of the subject to be subjected to detailed photographing is set in the schematic image (front image).

  In the field of dentistry, the dental optical diagnostic device handpiece is provided with OCT means, and the means for positioning the optical diagnostic location of the tooth part is an imaging method using a camera, and an imaging camera for acquiring a surface image is provided inside. (See Patent Document 2). Therefore, a camera image can be used for prior positioning. The image information acquired by the OCT means is recorded in association with patient personal information such as which tooth of which patient. In general, in a dental clinic, an electronic medical record is managed so that a tooth profile or the like can be displayed on a monitor by, for example, converting a patient's oral condition into an electronic file (see, for example, Patent Document 3). The processing apparatus described in Patent Literature 3 constitutes a tooth number input means by a control device and a display means. Then, when the tooth number designation window is displayed on the screen of the display device, when the operator performs an operation of inputting the tooth number, the tooth is schematically displayed in the oral state display window displayed on the display device by the control device. Displayed in the tooth profile diagram. This tooth number designation window divides the dentition into upper and lower jaws, and further separates the left and right sides of the midline into four blocks for entering tooth number numbers and symbols, and for permanent and deciduous teeth. For each.

JP 2010-142428 A Utility Model Registration No. 3118718 Japanese Patent Laid-Open No. 2003-61988

  However, in the conventional dental optical coherence tomographic image generation apparatus, it takes time and effort to input the tooth number and symbol. For example, there are usually 32 teeth for adults and 20 teeth for infants, so there is a possibility that it is wrong to input which tooth was photographed and which tooth is being treated. It was. Therefore, improvement in operability is desired.

  Therefore, in the present invention, a control apparatus, a control method, and a control method for a dental optical coherence tomographic image generation apparatus capable of solving the above-described problem and reducing the trouble of inputting the tooth number of the subject and managing the subject image as a file. It is an object to provide a control program.

  In order to solve the above problems, a control device for a dental optical coherence tomographic image generation device according to the present invention is an optical including a light source that periodically irradiates a subject with laser light and a detector that detects internal information of the subject. A unit, a scanning mechanism for two-dimensionally scanning the laser beam, a probe for guiding the laser beam from the optical unit to the subject and guiding the light reflected by the subject to the optical unit, and in synchronization with the laser beam A control device that performs imaging by controlling the scanning mechanism and generates a light coherence tomographic image of the subject from data obtained by converting a detection signal of the detector, and a display device that displays the optical coherence tomographic image A control unit of the dental optical coherence tomographic image generation apparatus comprising the control unit, and a predetermined imaging mode based on an external input An imaging control unit that performs imaging, an image processing unit that performs image processing on the detection signal acquired by imaging, and a file that creates patient file information for file management of personal information for each patient and captured image information of the subject And a storage means for storing tooth position information used in common for each patient in which tooth numbers according to a predetermined tooth type and positions of upper and lower dental arches are associated in advance and the patient file information. The file creation processing means, before photographing, an image display field for displaying an image of a dental arch, a display field of a tooth list table having a tooth number item for all teeth and a photographing target tooth number item, When a predetermined tooth in the displayed image of the dental arch is selected on the display device, an imaging region display screen for each patient including a single screen is displayed on the display device. Specify tooth number An input support processing means for performing processing for associating the identified tooth number with the tooth number to be imaged in the tooth list in association with the patient file information and the photographing date and time, An image display field for displaying an image of a row bow and a display field for displaying a patient file list for a designated patient are displayed on the display device by displaying on the display device a file selection screen for each patient. When a predetermined tooth in the dental arch image is selected, the tooth number of the tooth is specified based on the tooth position information, and the corresponding patient file in the patient file list is extracted and displayed. When processing is performed and a predetermined patient file in the patient file list is selected, based on the tooth position information, identify the tooth of the tooth number in the dental arch image, Imaging portion confirmation display processing means for performing processing for extracting and displaying the identified tooth.

  According to such a configuration, the control device of the dental optical coherence tomographic image generation device causes the input support processing means to display the imaging region display screen for each patient on the display device before imaging, and from the dental arch displayed on the screen. When a tooth is selected, the tooth number of the tooth is recorded and associated with the tooth list displayed on the screen simultaneously with the dental arch. Here, the operation of selecting a tooth from the dental arch is performed by the user clicking the mouse, which is a pointing device, on the GUI screen. This saves the trouble of inputting the tooth number and symbol and improves operability. In addition, the control unit for the dental optical coherence tomographic image generation device displays the image when the tooth is selected from the dental arch side on the file selection screen displayed after imaging by the imaging region confirmation display processing unit. The corresponding file is extracted from the patient file list and displayed. On the other hand, if the tooth number is specified from the selection of the patient file list, the tooth is extracted from the dental arch and displayed. Accordingly, the user can intuitively understand the correspondence between the image information associated with the patient file information created by photographing and the tooth number of the tooth in the dental arch displayed on the screen. .

  Further, in the control device for a dental optical coherence tomographic image generation device according to the present invention, the imaging region confirmation display processing means has a predetermined tooth or tooth number on the file selection screen displayed on the display device after imaging. When is selected, it is preferable to further perform processing for displaying the captured image information of the selected tooth or tooth number in the file selection screen based on the patient file information.

  According to such a configuration, the control device of the dental optical coherence tomographic image generation device also includes the captured image information corresponding to the tooth or tooth number selected on the imaging region display screen by the imaging region confirmation display processing unit after imaging. Therefore, the user can intuitively grasp the correspondence between the photographed tooth image, the position on the dental arch displayed on the screen, and the tooth number.

  In the control apparatus for a dental optical coherence tomographic image generation apparatus according to the present invention, the imaging control unit scans the imaging target range of the subject at a predetermined pitch with the scanning mechanism in order to measure internal information of the subject. Shooting is started when it is determined that an input of a measurement instruction to be received is received, and shooting is finished at a shooting time corresponding to the predetermined pitch, and the shooting target range is set to the scanning mechanism from the predetermined pitch. Shooting is started when it is determined that an input of a preview instruction for scanning at a coarse pitch has been received, and second shooting control means for ending shooting when it is determined that an input of an instruction to cancel the preview instruction is received. It is preferable to provide.

  According to this configuration, the control device of the dental optical coherence tomographic image generation device starts photographing the subject when the first photographing control unit receives an input of a measurement instruction, and the scanning mechanism scans at a predetermined pitch. The detection signal acquired in this manner is image-processed by the image processing means, thereby displaying an optical coherence tomographic image of the subject on the display device with a predetermined resolution. At this time, since the photographing is finished with the photographing time corresponding to the scanning pitch of the scanning mechanism, the still image of the optical coherence tomographic image is displayed on the display device after the photographing is finished. In addition, the control device of the dental optical coherence tomographic image generation device starts photographing the subject when the second photographing control unit receives an input of a preview instruction, and the scanning mechanism scans at a pitch coarser than a predetermined pitch. The detection signal acquired in this manner is image-processed by the image processing means, so that the optical coherence tomographic image of the subject is displayed on the display device at a resolution lower than the predetermined resolution. At this time, the optical coherence tomographic image displayed by the preview instruction uses the detection signals scanned at a coarser pitch than the optical coherence tomographic image displayed by the measurement instruction, and therefore can be displayed at high speed. Further, since the low-resolution optical coherence tomographic image continues to be imaged and processed until an input of an instruction to cancel the preview instruction is received, the imaged optical coherence tomographic image can be displayed as a real-time image. Note that the resolution does not change in the direction along the optical axis of the subject.

  Further, in the control device for a dental optical coherence tomographic image generation device according to the present invention, the image processing means is irradiated with the laser light as a two-dimensional image of a scan plane in a direction perpendicular to the optical axis of the subject. On-face image generation means for generating an on-face image that is an image obtained by combining information on the surface of the subject and information on the direction along the optical axis of the subject, and the on-face image displayed on the display device A tomographic position line generation unit that draws and superimposes a tomographic position of an optical coherence tomographic image on a line, and receives an instruction to select and move the line of the tomographic position displayed on the display device. Optical coherence tomographic image generation means for generating the optical coherence tomographic image from data obtained by converting the detection signal of the detector based on the information. It is preferred.

  According to such a configuration, the control device for the dental optical coherence tomographic image generation device converts the information on the surface of the subject and the optical axis of the subject as a two-dimensional image of the scan plane by the on-face image generation unit of the image processing unit. An on-face image, which is an image combined with information in the direction along, is generated. This on-face image is generated using not only information on the outer surface of the subject but also internal information as data obtained by image processing of a signal detected by OCT. Therefore, an on-face image can be used for measurement and diagnosis. Further, the control device of the dental optical coherence tomographic image generation apparatus draws and superimposes the tomographic position of the optical coherent tomographic image in a line shape on the on-face image by the tomographic position line generation unit of the image processing unit. Thereby, an on-face image can be used as an image showing a tomographic position. In addition, the control device of the dental optical coherence tomographic image generation apparatus receives selection and movement instructions for the displayed line of the tomographic position by the optical coherent tomographic image generation unit of the image processing unit, and the tomographic position specified by the line An optical coherence tomographic image is generated. Here, the selection and movement instructions for the line are performed by the user on the GUI screen using a pointing device or the like. Further, according to such a configuration, it is not necessary to provide a member such as a dedicated camera for acquiring an image showing the tomographic position in the dental optical coherence tomographic image generation apparatus. Therefore, for example, there is no need to provide a CCD camera, a CMOS camera, or the like in the probe, so that the probe can be reduced in size.

  The dental optical coherence tomographic image generating apparatus control method according to the present invention includes an optical unit including a light source that periodically irradiates a subject with laser light, a detector that detects internal information of the subject, and the laser. Including a scanning mechanism for two-dimensionally scanning light, a probe for guiding laser light from the optical unit to the subject and guiding light reflected by the subject to the optical unit, and controlling the scanning mechanism in synchronization with the laser light And a control unit including a control device that performs control to generate an optical coherence tomographic image of the subject from data obtained by imaging and converting the detection signal of the detector, and a display device that displays the optical coherence tomographic image, A method for controlling a dental optical coherence tomographic image generation apparatus comprising: a personal information for each patient and a photographed image information of the subject. Storage means for storing patient file information for managing, and tooth position information used in common with each patient in which tooth numbers according to a predetermined tooth type and positions of upper and lower dental arches are associated in advance, and before imaging An image display field for displaying an image of a dental arch and a display field of a tooth list having a tooth number item for all teeth and an item for a tooth number to be photographed on one screen. When the display device displays a screen and a predetermined tooth in the displayed image of the dental arch is selected, the tooth number of the tooth is specified based on the tooth position information, and the patient file information and A step of performing processing for associating the identified tooth number with the tooth number to be photographed in the tooth list in association with the photographing date and time, and displaying the dental arch image after photographing. Column and the designated patient A display field for displaying a list of patient files of each patient, and a file selection screen for each patient including a single screen on the display device, and when a predetermined tooth in the displayed image of the dental arch is selected Identifying the tooth number of the tooth based on the tooth position information, extracting the patient file in the patient file list and displaying the patient file, and displaying the display on the display device after imaging In the file selection screen, when a predetermined patient file in the patient file list is selected, the tooth of the tooth number is specified in the dental arch image based on the tooth position information, and the specified tooth And performing a process of extracting and displaying the process.

  According to such a procedure, the control method of the dental optical coherence tomographic image generation device is such that, before imaging, the control device displays an imaging region display screen for each patient on the display device, and the tooth is displayed from the dental arch displayed on the screen. When selected, the tooth number of the tooth is recorded, and a process of associating with the tooth list displayed on the screen simultaneously with the dental arch is performed. This saves the trouble of inputting the tooth number and symbol and improves operability. Then, in the file selection screen displayed on the display device by the control device after imaging, if a tooth is selected from the dental arch side, the corresponding file is extracted from the displayed patient file list and displayed. On the other hand, when the tooth number is specified from the selection of the patient file list, the tooth is extracted from the dental arch and displayed. Accordingly, the user can intuitively understand the correspondence between the image information associated with the patient file information created by photographing and the tooth number of the tooth in the dental arch displayed on the screen. .

  The dental optical coherence tomographic image generation device control program according to the present invention is a program for causing a computer to function as each unit of the control device of the dental optical coherence tomographic image generation device. By being configured in this way, a computer in which this program is installed can realize each function based on this program.

  According to the present invention, the control device of the dental optical coherence tomographic image generation device can manage the image of the subject as a file while reducing the effort of inputting the tooth number of the subject. Further, according to the present invention, the operability is improved for the user, and the correspondence between the position of the photographed tooth and the tooth number can be easily grasped in the dental arch displayed on the screen of the display device. There is an effect.

BRIEF DESCRIPTION OF THE DRAWINGS It is an external view of the dental optical coherence tomographic image generation apparatus which concerns on embodiment of this invention, Comprising: (a) has shown the single joint arm type | mold, (b) has shown the articulated arm type | mold, respectively. It is a block diagram which shows typically the unit structure of the dental optical coherence tomographic image generation apparatus which concerns on embodiment of this invention. It is a block diagram which shows the function of the OCT control apparatus which concerns on embodiment of this invention. It is explanatory drawing of imaging | photography by the dental optical coherence tomographic image generation apparatus which concerns on embodiment of this invention, Comprising: (a) is a figure which shows the kind of recording area, (b) is the optical path of the laser beam inside a diagnostic probe. A schematic diagram is shown respectively. It is explanatory drawing of the production | generation process of the OCT image by the OCT control apparatus which concerns on embodiment of this invention. It is a flowchart which shows the flow of the arithmetic processing for the OCT control apparatus which concerns on embodiment of this invention to display an OCT image. It is a flowchart which shows the flow of the arithmetic processing for the OCT control apparatus which concerns on embodiment of this invention to display an on-face image. It is an example of the timing chart of the image processing by the OCT control apparatus which concerns on embodiment of this invention, Comprising: (a) is a scanning trigger of a light source output, (b) is a start trigger of DA conversion circuit output, (c) and (d ) Indicates analog output voltages in the X and Y directions by the galvanomirror control circuit, and (e) indicates a clock for generating an OCT image. It is a flowchart (the 1) which shows the flow of the online process by the OCT control apparatus which concerns on embodiment of this invention. It is a flowchart (the 2) which shows the flow of the online process by the OCT control apparatus which concerns on embodiment of this invention. It is a flowchart which shows the flow of the offline process by the OCT control apparatus which concerns on embodiment of this invention. It is a figure which shows an example of the main menu (start screen) which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the patient information input screen which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the online display screen which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the test | inspection (online) screen which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the patient search screen (offline) which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the file selection screen (offline) which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows the other example of the file selection screen (offline) which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus. It is a figure which shows an example of the offline display screen which the OCT control apparatus which concerns on embodiment of this invention displays on a display apparatus.

  DESCRIPTION OF EMBODIMENTS Hereinafter, an embodiment for implementing an apparatus of the present invention (hereinafter referred to as “embodiment”) will be described in detail with reference to the drawings. In the following, 1. 1. Outline of OCT apparatus configuration 2. Configuration of OCT control device 3. Operation of OCT controller This will be described in detail in each chapter of screen display examples of the display device.

[1. Overview of OCT system configuration]
The outline of the configuration of the OCT apparatus (dental optical coherence tomographic image generation apparatus) will be described with reference to FIGS. 1 and 2 on the assumption that a subject to be imaged by the OCT apparatus is a tooth to be diagnosed by a dental patient. As shown in FIGS. 1 and 2, the OCT apparatus 1 mainly includes an optical unit section (optical unit) 10, a diagnostic probe section (probe) 30, and a control unit section (control unit) 50.

<Optical unit section>
The optical unit (optical unit) 10 includes a light source, an optical system, and a detection unit to which each method of general optical coherence tomography can be applied. As shown in FIG. 2, the optical unit 10 includes a light source 11 that periodically irradiates a sample (subject) S with laser light, a detector (detector) 23 that detects internal information of the sample S, and a light source 11. An optical fiber and various optical components provided in the optical path between the detector 23 and the like are provided.

Here, an outline of the optical unit unit 10 will be described.
The light emitted from the light source 11 is divided into measurement light and reference light by a coupler 12 which is a light dividing means. The measurement light enters the diagnostic probe unit 30 from the circulator 14 of the sample arm 13. This measurement light is condensed on the sample S by the condenser lens 34 through the collimator lens 32 and the galvanometer mirror (scanning mechanism) 33 when the shutter 31 of the diagnostic probe unit 30 is open, and is collected again after being scattered and reflected there. It returns to the circulator 14 of the sample arm 13 through the optical lens 34, the galvanometer mirror 33, and the collimator lens 32. The returned measurement light is input to the detector 23 via the coupler 16.

  On the other hand, the reference light separated by the coupler 12 passes through the collimator lens 19 from the circulator 18 of the reference arm 17 and is condensed on the reference mirror 21 by the condenser lens 20, and after being reflected there, is again collected into the condenser lens 20 and the collimator lens 19. After that, the flow returns to the circulator 18. The returned reference light is input to the detector 23 via the coupler 16. That is, since the coupler 16 combines the measurement light scattered and reflected by the sample S and the reference light reflected by the reference mirror 21, the detector 23 detects the light (interference light) interfered by the combination. It can be detected as internal information of the sample S. Note that the polarization controller 15 of the sample arm 13 and the polarization controller 22 of the reference arm 17 are each installed to return the polarized light generated inside the OCT apparatus 1 including the diagnostic probe unit 30 to a state with less polarization. ing.

As the light source 11, for example, a laser light source for SS-OCT method can be used.
In this case, it is preferable that the light source 11 has a performance with a center wavelength of 1310 nm, a sweep wavelength width of 100 nm, a sweep speed of 50 kHz, and a coherence distance (coherent length) of 14 mm. Here, the coherent distance corresponds to a distance when the attenuation of the power spectrum is 6 dB. The coherent distance is preferably a highly coherent distance of 10 mm or more and less than 48 mm, but is not limited thereto.

<Diagnostic probe part>
The diagnostic probe unit (probe) 30 includes a galvanometer mirror (scanning mechanism) 33 that two-dimensionally scans the laser beam, guides the laser beam from the optical unit unit 10 to the sample S, and reflects the light reflected by the sample S to the optical unit. It leads to the part 10.

  The diagnostic probe unit 30 is connected to the optical unit unit 10 and the control unit unit 50 by a cable 60 (see FIG. 1). The cable 60 includes an optical fiber connected to the optical unit unit 10 and a communication line connected to the control unit unit 50.

  At times other than during imaging, the diagnostic probe unit 30 is attached to the tip of the single joint arm 70 extending in the horizontal direction from the lower side of the display device 54 disposed at the upper portion of the OCT apparatus 1 as shown in FIG. Hold it in the holder. Thereby, at the time of accommodation, even if it is the long cable 60, it can accommodate without twisting a cable, and a storage space can be reduced.

  On the other hand, at the time of imaging, the user removes and grasps the diagnostic probe unit 30 from the holder of the single joint arm 70 and brings the diagnostic probe unit 30 into contact with the patient to prevent camera shake. At this time, the foot controller 80 (see FIG. 1) connected to the control unit 50 in a wired or wireless manner can be used to operate the photographing start button even if both hands of the user are blocked.

  When the OCT apparatus 1A shown in FIG. 1B is not in the middle of imaging, the diagnostic probe unit 30 includes an articulated arm 70A that extends horizontally from the upper side of the display device 54 disposed on the OCT apparatus 1A. The OCT apparatus 1 is the same as the OCT apparatus 1 shown in FIG. 1A except that it can be held by the tip holder. The articulated arm 70A has a longer length from the base end to the distal end holder than the single articulated arm 70, and is arranged at a higher position from the floor. Therefore, the drooping of the cable 60 can be reduced. As a merit that the cable 60 does not reach the floor in this way, a sanitary point can be mentioned. This also improves operability and prevents the cable 60 that has dropped from being stepped on by mistake.

  Specifically, as shown in FIG. 4B, the galvano mirror 33 provided in the diagnostic probe unit 30 is provided with an X-direction galvanometer mirror 33X and a Y-direction galvanometer mirror 33Y. Laser light emitted from the light source 11 is applied to the sample S (see FIG. 2; the same applies hereinafter) via the X-direction galvanometer mirror 33X and the Y-direction galvanometer mirror 33Y, and the nozzle tip of the diagnostic probe unit 30 (FIG. 4). The detector 23 obtains internal information in the depth direction (A direction) that proceeds inward from the surface of the sample S facing the left end in (b). As will be described later, data in the A direction consisting of 1152 points (hereinafter referred to as A line data) is acquired in one scan, and then image processing (FFT processing) of frequency analysis is performed to perform FFT processing of the data in the A direction. As a result, each data of 1024 points (hereinafter referred to as A line (1024 points FFT)) is acquired.

  Here, the X direction and the Y direction refer to the lateral direction (X axis direction, X axis direction, Y) on the surface of the sample S (see FIG. 4A) that the nozzle tip of the diagnostic probe unit 30 (the left end in FIG. 4B) faces directly. This corresponds to the horizontal direction in FIG. 4A and the vertical direction (Y-axis direction, vertical direction in FIG. 4A).

  The X-direction galvanometer mirror 33X is provided on the collimator lens 32 side. The X-direction galvanometer mirror 33X rotates a mirror surface (A-V plane) by motor drive with the A direction as an axis. At this time, the direction of the acquired data is data in the horizontal direction (X-axis direction) on the surface of the sample S, and is data in the B direction. If the operation rotation angle of the galvano mirror is, for example, -3 ° to + 3 ° and 128-point B-direction data is required, 158-point B-direction data (hereinafter referred to as B-line data) is acquired as described later. .

  The Y-direction galvanometer mirror 33Y is provided on the condensing lens 34 side, and rotates the mirror surface (BV plane) by motor drive with the B direction as an axis. At this time, the direction of the acquired data is data in the vertical direction (Y-axis direction) on the surface of the sample S, and is data in the V direction (hereinafter referred to as V line data).

<Control unit section>
As shown in FIG. 2, the control unit unit (control unit) 50 includes an AD conversion circuit 51, a DA conversion circuit 52, a galvano mirror control circuit 53, a display device 54, and an OCT control device 100.

  The AD conversion circuit 51 converts an analog output signal of the detector (detector) 23 into a digital signal. In the present embodiment, the AD conversion circuit 51 starts acquisition of a signal in synchronization with a trigger output from the laser output device that is the light source 11, and the timing of the clock signal ck that is also output from the laser output device. At the same time, the analog output signal of the detector (detector) 23 is acquired and converted into a digital signal. This digital signal is input to the OCT controller 100.

  The DA conversion circuit 52 converts the digital output signal of the OCT control apparatus 100 into an analog signal. In the present embodiment, the DA conversion circuit 52 converts the digital signal of the OCT control device 100 into an analog signal in synchronization with a trigger output from the laser output device that is the light source 11. This analog signal is input to the galvanometer mirror control circuit 53.

  The galvanometer mirror control circuit 53 is a driver that controls the galvanometer mirror 33 of the diagnostic probe unit 30. The galvano mirror control circuit 53 drives the motor of the X direction galvano mirror 33X or the Y direction galvano mirror 33Y in synchronization with the output period of the laser emitted from the light source 11 based on the analog output signal of the OCT control device 100. Alternatively, a motor drive signal for stopping is output.

  The galvano mirror control circuit 53 performs processing for changing the angle of the mirror surface by rotating the axis of the X direction galvano mirror 33X, and processing for changing the angle of the mirror surface by rotating the axis of the Y direction galvano mirror 33Y. Do it at different times. These processes of the galvanometer mirror control circuit 53 are simply referred to as galvanometer mirror X and Y axis changes. An example of timing for changing the galvanometer mirror X and Y axes will be described later.

  The display device 54 displays an optical coherence tomographic image (hereinafter referred to as an OCT image) generated by the OCT control device 100. The display device 54 includes, for example, a liquid crystal display (LCD), an EL (Electronic Luminescence), a CRT (Cathode Ray Tube), a PDP (Plasma Display Panel), and the like.

  The OCT control apparatus 100 is a control apparatus for the OCT apparatus 1 and performs imaging by controlling the galvanometer mirror 33 in synchronization with the laser beam, and also converts the detection signal of the detector 23 into an OCT image of the sample S. The control which produces | generates is performed.

[2. Configuration of OCT controller]
As shown in FIG. 3, the OCT control apparatus 100 includes a computer including an input / output unit 110, a storage unit 120, and a calculation unit 130, and a program installed in the computer.

The input / output unit 110 is an interface that transmits and receives various types of information to and from the outside.
The storage unit 120 stores prestored data such as the above-described program, patient personal information 122 input from the input device M such as a mouse, calculation processing results (for example, image information 123) by the calculation unit 130, and other various types of information. For this purpose, a memory such as a RAM (Random Access Memory) and a ROM (Read Only Memory), a hard disk, and the like are provided.

In the example illustrated in FIG. 3, the storage unit 120 stores tooth position information 124 and image window display data 125.
The tooth position information 124 indicates information in which a tooth number according to a predetermined tooth type is associated with the positions of the upper and lower dental arches in advance.
The image window display data 125 indicates display data used for screen display as shown in FIGS. Each screen will be described later.
The tooth position information 124 and the image window display data 125 are information commonly used for each patient.

  The calculation means 130 is composed of, for example, a CPU (Central Processing Unit), a GPU (Graphics Processing Unit), and the like, and includes a photographing control means 140, an image processing means 150, and a file creation processing means 160.

  The imaging control unit 140 performs imaging in a predetermined imaging mode based on an external input. The imaging control unit 140 includes a first imaging control unit 141, a second imaging control unit 142, and a scanning area selection control unit. 143.

  The first imaging control unit 141 starts imaging when it is determined that an input of a measurement instruction for scanning the imaging target range of the sample S at a predetermined pitch is received by the galvanometer mirror 33 in order to measure the internal information of the sample S. Control for ending the shooting at the shooting time corresponding to the predetermined pitch is performed. The first photographing control unit 141 causes the image processing unit 150 to perform image processing on the detection signal acquired by photographing. Based on this measurement instruction, the image processing means 150 performs image processing on the detection signal obtained by scanning the galvano mirror 33 at a predetermined pitch, thereby displaying the optical coherence tomographic image of the sample S on the display device 54 at a predetermined resolution. can do. The mode that operates according to this measurement instruction is one of the predetermined shooting modes.

In the present embodiment, the imaging mode includes three measurement modes of 200 measurement, 300 measurement, and 400 measurement as an example when the light source 11 has a sweep speed of 50 kHz.
At the time of 200 measurement, A line data is acquired at a point of 200 × 200 pixels corresponding to the surface of the sample S, and the image information is displayed.
At the time of 300 measurement, A line data is acquired at a point of 300 × 300 pixels corresponding to the surface of the sample S, and the image information is displayed.
At 400 measurement, A line data is acquired at a point of 400 × 400 pixels corresponding to the surface of the sample S, and the image information is displayed.
Here, the detection signal acquired by photographing in one of the measurement modes is subjected to image processing by the image processing means 150.

  The second shooting control unit 142 starts shooting when it determines that it has received an input of a preview instruction to cause the galvano mirror 33 to scan the shooting target range at a pitch coarser than the predetermined pitch, and inputs an instruction to cancel the preview instruction When it is determined that an image has been received, control for ending the shooting is performed. The second photographing control unit 142 causes the image processing unit 150 to perform image processing on the detection signal acquired by photographing. Based on the preview instruction, the detection signal obtained by scanning the galvano mirror 33 at a pitch coarser than the predetermined pitch is subjected to image processing by the image processing means 150, whereby the sample S is scanned at a resolution lower than the predetermined resolution. The optical coherence tomographic image can be displayed on the display device 54. Note that the low-resolution image displayed by the preview instruction is the same as the resolution in the measurement mode in the direction along the optical axis in the sample S (data in the A direction). The mode that operates in response to the preview instruction is one of predetermined shooting modes.

Hereinafter, this mode is referred to as a preview mode.
In the present embodiment, the preview mode acquires A line data at points of, for example, 128 × 128 pixels corresponding to the surface of the sample S when the light source 11 has a sweep speed of 50 kHz, and displays the image information. In the present embodiment, the preview mode is terminated when any of the measurement modes is entered by the above-described measurement instruction. That is, the instruction to cancel the preview instruction is also used as the measurement instruction.

  Although details will be described later, in this embodiment, the operation button “Preview” (see FIG. 15) on the GUI screen or the operation button “Measure” (see FIG. 15) is clicked with the input device M such as a mouse. A preview instruction or a measurement instruction can be input to the imaging control unit 140.

  In the present embodiment, a preview instruction or a measurement instruction can be input to the imaging control unit 140 from the foot controller 80 that is connected to the control unit 50 so as to be wired or wirelessly communicable. Specifically, the foot controller 80 notifies the imaging control means 140 of the first-stage and second-stage switch signals corresponding to the depression when the user steps on the first and second stages. Thus, when the second imaging control unit 142 receives the input of the first-stage switch signal from the foot controller 80, the second imaging control unit 142 determines that the input of the preview instruction is received, and receives the input of the second-stage switch signal. It is determined that an instruction to cancel the preview instruction has been received. Further, the first imaging control unit 141 determines that the input of the measurement instruction has been received when the input of the second-stage switch signal is received from the foot controller 80. At the time of actual photographing, the user needs to bring the diagnostic probe unit 30 into contact with the patient in order to prevent camera shake, etc., but the user's hands are blocked by controlling the foot controller 80 in this way. Even if the foot controller 80 is stepped on with a foot, a preview instruction or a measurement instruction can be input. Note that the present invention is not limited to the two-stage method.

  The scanning area selection control unit 143 accepts an input of an area selected by the user from a plurality of areas having different predetermined areas as the imaging target range of the sample S, and the galvano mirror 33 according to the accepted area. The control for selecting the scanning range is performed. The scanning area selection control unit 143 outputs a control signal (analog signal) synchronized with the output period of the laser emitted from the light source 11 to the galvanometer mirror control circuit 53.

  In the example shown in FIG. 4A, as the range scanned by the galvanometer mirror 33, the surface of the sample S is the narrowest range (S: small), the middle range (M: middle), and the widest range (L: large). ) Can be selected from three stages. In this case, the operation rotation angles of the X-direction galvanometer mirror 33X and the Y-direction galvanometer mirror 33Y are set in a range of, for example, -1 ° to + 1 °, a range of -2 ° to + 2 °, and a range of -3 ° to + 3 °. By doing so, it is possible to designate a recording area in three stages of SML.

The image processing means 150 performs image processing on the detection signal acquired by photographing.
The image processing unit 150 obtains an OCT image of the tomographic plane in the direction along the optical axis in the sample S and a two-dimensional image of the scan plane in the direction perpendicular to the optical axis of the sample S from the data acquired by photographing the sample S. And a 3D image of the sample S are generated, and control is performed to display each generated image as image information of the sample S on a one-screen display of the display device 54. For this purpose, as shown in FIG. 3, the image processing unit 150 includes an on-face image generation unit 151, an OCT image generation unit 152, a rendering unit 153, and a tomographic position line generation unit 154.

The on-face image generation means 151 includes information on the surface of the sample S irradiated with the laser light and the light in the sample S as a two-dimensional image of the scan plane in the direction (B direction, V direction) perpendicular to the optical axis in the sample S. An on-face image, which is an image combined with information in a direction along the axis (direction A), is generated.
In the present embodiment, the on-face image generation unit 151 averages the values indicated by the respective data (A-line data described later) in the direction along the optical axis in the sample S acquired by photographing the sample S. The on-face image is generated by obtaining each of the two-dimensional directions scanned by the galvanometer mirror 33. The generated on-face image is displayed on the display device 54. The process flow for generating an on-face image will be described later. As will be described later, a 3D image of the sample S is generated in the process of generating the on-face image.

  The OCT image generation unit 152 generates an OCT image (optical coherence tomographic image) of a tomographic plane in the direction along the optical axis in the sample S from data acquired by photographing the sample S. The generated OCT image is displayed on the display device 54. The process flow for generating the OCT image will be described later.

The rendering unit 153 creates a 3D image of the designated sample S from the data stored in the storage unit 120 after shooting, and displays the 3D image on the display device 54.
The tomographic position line generation unit 154 draws and superimposes the tomographic position of the OCT image in a line on the on-face image displayed on the display device 54.
In the present embodiment, the OCT image generation unit 152 receives an instruction for selection and movement with respect to the line of the tomographic position generated by the tomographic position line generation unit 154, and based on the information of the selected and moved line, the detector 23 An OCT image is generated from the data obtained by converting the detection signal.

  The file creation processing means 160 creates a patient file 121 for file management of patient-specific personal information and image information 123 (see FIG. 3) obtained by photographing the sample S. The file creation processing unit 160 includes an input support processing unit 161 and an imaging region confirmation display processing unit 162.

  The input support processing means 161 performs processing for supporting the user's input operation before imaging, and displays an imaging region display screen for each patient including a dental arch and a tooth list on one screen. 54, when a tooth is selected from the dental arch, the tooth number is input. The mode operated by this input operation is an input mode in online processing described later. Here, the imaging region display screen refers to a screen that is displayed, for example, by overlapping the “dental and tooth number” windows on the online display screen shown in FIG. In this example, the “dental formula and tooth number” window has an image display field for displaying an image of the dental arch on the right side in FIG. 14, and items of the tooth numbers of all teeth and photographing on the left side in FIG. 14. And a display column of a tooth list having a target tooth number item.

  When a predetermined tooth in the displayed dental arch image is selected, the input support processing unit 161 identifies the tooth number of the tooth based on the tooth position information 124 (see FIG. 3), and the patient file 121 The image is stored in the storage unit 120 in association with the shooting date and time. The mode that operates in this saving operation is a saving mode in online processing described later. At this time, the input support processing unit 161 performs processing for associating the identified tooth number with the imaging target tooth number in the tooth list. By this association, the identified tooth number is highlighted in the tooth list displayed on the screen. The highlighting method is not particularly limited. For example, in the example shown in FIG. 14, a mark is additionally displayed on the corresponding line. For example, the entire corresponding line or a part of the line may be highlighted by hatching or color.

  In the example shown in FIG. 14, the user clicks the lower right first tooth indicated by hatching in the dental arch, and in the tooth list table, a mark (double The inside of the circle is filled). As a result, the input support processing unit 161 registers information indicating that the tooth number of the part to be imaged is the lower right number 1 in the patient file 121 as a part of the patient personal information 122. In this example, in the tooth list, there are three methods: Zsigmondy & Palmer system (hereinafter referred to as Zsigmondy method), FDI system (FDI World Dental Federation notation: hereinafter referred to as FDI method), and Universal numbering system (hereinafter referred to as universal method). The pattern can be selected. In FIG. 14, the Zsigmondy method is selected as shown by a double circle as an example. Therefore, in the position item of the tooth list, the upper right tooth number is displayed as “1, 2,..., 8, A,. These tooth numbers correspond to the FDI system “11, 12,..., 18, 51,. Incidentally, when the universal method is selected, although not shown, the upper right tooth number is “8, 7,..., 1, E,. In this embodiment, it is possible to select a plurality of teeth. In the conventional apparatus, it is necessary for the user to input the tooth number and symbol in the window for specifying the tooth number. However, according to the present embodiment, it is not necessary to input the number and symbol. . Further, since the user selects a tooth from the dental arch, the user can intuitively grasp the correspondence between the position of the tooth and the tooth number.

  The imaging part confirmation display processing unit 162 assists the user in searching for stored image information of the imaging part after imaging, and performs a process of displaying the image information for confirmation. The mode operated by this search operation is a search mode in offline processing described later. The imaging part confirmation display processing means 162 displays a file selection screen for each patient including the dental arch and a patient file list for the designated patient on one screen on the display device 54, and the tooth in the dental arch A process for displaying the patient file in association with the patient file is performed. An example of the file selection screen is shown in FIG. In this example, an image display field for displaying an image of a dental arch is provided in the center on the right side in FIG. 17, and a display field for a patient file list for each imaging date and site is provided on the left side in FIG.

  When a predetermined tooth in the displayed dental arch image is selected, the imaging part confirmation display processing unit 162 identifies the tooth number of the tooth based on the tooth position information 124 (see FIG. 3), and the patient Extract the patient file from the file list and display it. In the example shown in FIG. 17, when the user clicks the lower right first tooth indicated by hatching in the dental arch, as indicated by hatching in the patient list, the corresponding “imaging site is lower right 1”. All (four in this example) patient files are extracted and highlighted. Thus, the user can intuitively grasp the correspondence relationship between the tooth information of the image information 123 associated with the patient file 121 created by photographing in the dental arch displayed on the screen. it can.

  Here, as illustrated in the patient file list, there may be a case where the imaging portion of “lower right 1” is imaged twice a day, and there may be image information on different imaging dates for the same patient. Of course, there are cases where the user (doctor) intends to continuously observe the imaging data on different imaging days in order to examine the progress of the site to be treated. In the patient list, when the imaging data (patient file item information) is arranged in a simple date order, for example, the information of “lower right 1” in the patient list is usually displayed at discrete positions. However, by extracting and highlighting as shown by hatching in the patient list of FIG. 17, the user can easily pick up desired imaging data.

  In another example shown in FIG. 18, when the user clicks on the lower right first tooth indicated by hatching in the dental arch, as indicated by hatching in the patient list, the corresponding “imaging region” Are all 4 (in this example, 4) patient files that are extracted and highlighted. As a result, the imaging data of the tooth clicked by the user on the dental arch and the non-existing imaging data are separated, so that the user can easily pick up desired imaging data. Note that the method of extracting and highlighting the corresponding patient file is not limited to that shown in FIGS. 17 and 18. For example, the entire corresponding line may be highlighted by hatching or color, but only a part of the corresponding line may be highlighted. Further, a mark may be additionally displayed on the corresponding line.

  Similarly, when a predetermined patient file in the displayed patient file list is selected, the imaging region confirmation display processing unit 162 selects an image of the dental arch based on the tooth position information 124 (see FIG. 3). The tooth of the tooth number is specified, and the specified tooth is extracted from the dental arch and displayed. In the example shown in FIG. 17 and FIG. 18, when the user clicks one of the patient files indicated by hatching in the patient file, the first right lower tooth in the dental arch has a hatch indicating that it has been selected. It is displayed. Note that the method of extracting and displaying the corresponding tooth in the dental arch may be to highlight the tooth by hatching or color as shown in FIG. 17 and FIG. A mark may be additionally displayed.

  Further, in this embodiment, the imaging region confirmation display processing unit 162 is based on the patient file 121 when a predetermined tooth or tooth number is selected on the file selection screen displayed on the display device 54 after imaging. A process of displaying the image information 123 of the selected tooth or tooth number in the file selection screen is further performed. The file selection screen shown in FIGS. 17 and 18 is provided with an image display field for displaying an on-face image of the lower right first tooth below the right side in FIGS. 17 and 18. Thereby, the user can grasp | ascertain intuitively the correspondence of the image | photographed tooth image, the position in the dental arch displayed on the screen, and the tooth number.

[3. Operation of OCT controller]
Here, regarding the operation of the OCT control apparatus 100, 3-1. Operation mode, 3-2. Outline of stereoscopic scanning 3-3. Specific example of stereoscopic scanning 3-4. On-face image generation processing, 3-5. Specific example of image processing timing, 3-6. Online processing flow, 3-7. This will be described in detail in each section of the offline processing flow.

<3-1. Operation mode>
The outline of the operation mode of the OCT control apparatus 100 of this embodiment is demonstrated.
≪Preview mode≫
The preview mode is a mode in online processing described later.
The OCT control apparatus 100 starts imaging when it is determined that an input of a preview instruction is received from the outside, and ends imaging when it is determined that an input of a measurement instruction is received. In addition, the OCT control apparatus 100 performs image processing on the detection signal acquired by photographing in the preview mode. FIG. 15 shows a screen display example on the display device 54. Although the process flow will be described later, FIG. 15 shows an inspection (online) screen. Here, the online screen refers to a screen that is displayed during online processing to be described later. As the connection state of the devices during online processing, the diagnostic probe unit 30-optical unit unit 10-control unit unit 50-display device 54 line is connected, and the information acquired by the diagnostic probe unit 30 is displayed as it is in real time. It can be displayed on the device 54.

≪Measurement mode≫
The measurement mode is a mode in online processing described later.
The OCT control apparatus 100 starts imaging when it is determined that an input of a measurement instruction has been received from the outside, and ends imaging at an imaging time corresponding to a predetermined pitch (200 measurement, 300 measurement, 400 measurement) of the galvano mirror 33. To do. In addition, the OCT control apparatus 100 performs image processing on the detection signal acquired by imaging in the measurement mode. FIG. 15 shows a screen display example on the display device 54. Although the process flow will be described later, FIG. 15 shows an inspection (online) screen.

≪Input mode≫
The input mode is an operation mode performed before the preview mode or the measurement mode in online processing. In the input mode, the OCT control apparatus 100 receives input of patient personal information 122 such as patient personal information and a tooth number to be imaged from the outside, and creates a patient file 121. The processing flow will be described later.

≪Save mode≫
The storage mode is an operation mode performed after the measurement mode in online processing. In the storage mode, the OCT control apparatus 100 receives an input of an operation for storing image information from the outside, and associates the patient personal information 122 with the captured image information 123 in the patient file 121. The processing flow will be described later.

≪Search mode≫
The search mode is an operation mode performed in offline processing after the storage mode. In the search mode, the OCT control apparatus 100 accepts an input of an operation for searching for image information from the outside, extracts desired image information 123 from the patient file 121 stored in the storage unit 120, and displays it on the display device 54. . The processing flow will be described later, but FIG. 19 shows an offline display screen. Here, the offline screen refers to a screen that is displayed during offline processing to be described later. At the time of offline processing, the information acquired by the diagnostic probe unit 30 is not displayed on the display device 54 as it is, but the information acquired by the above-described online processing and stored in the storage unit 120 is temporarily released from the online processing, Thereafter, the offline processing is started and then read out and displayed on the display device 54.

<3-2. Overview of stereoscopic scanning>
A procedure in which the OCT control apparatus 100 generates a two-dimensional OCT image and further performs a stereoscopic scan will be described with reference to FIGS. 5 and 6 (see FIG. 3 as appropriate).
The patient's teeth (sample S) are positioned in advance. Further, based on the user's operation, the scanning area selection control unit 143 determines the range to be scanned by the galvano mirror 33 from, for example, the ranges S, M, and L shown in FIG.

  The A line, the B line, and the V line shown in FIGS. 5A and 5B indicate directions along the A axis, the B axis, and the V axis of the diagnostic probe unit 30 shown in FIG. 4B. ing. 5A corresponds to data indicating tomographic information (internal information) in the depth direction from the surface of the sample S, and B line corresponds to data indicating internal information in the width direction of the sample S. To do. The V line shown in FIG. 5B corresponds to data indicating internal information of the sample S in the depth direction. If each data of A line, B line, and V line in a predetermined range is acquired, one volume of solid (3D) can be scanned.

  The OCT image generation means 152 of the image processing means 150 acquires A line data (step S1). The galvano mirror control circuit 53 appropriately changes the galvano mirror X and Y axes under the control of the scanning area selection control means 143 (step S2). An example of timing will be described later.

  Then, the OCT image generation means 152 determines whether or not one volume of A line data has been acquired (step S3). If one line of A line data has not yet been acquired (step S3: No), OCT image generation is performed. The means 152 returns to step S1. On the other hand, when one volume of A line data has been acquired (step S3: Yes), the OCT image generation unit 152 performs window processing (step S4). Subsequently, the OCT image generation unit 152 performs an FFT operation (step S5).

<3-3. Specific example of stereoscopic scanning>
Hereinafter, a specific example of stereoscopic scanning will be described.
In the present embodiment, for example, A line data of 1152 points is acquired. In this case, assuming a cubic virtual space (one side L) aligned with the position of the sample S positioned at the nozzle tip of the diagnostic probe unit 30, the 0th point indicating the nozzle-side outermost surface of the virtual space has a waveform. 1152 point A line data is acquired with the 1151st point indicating the data start point and the outermost surface on the depth side of the virtual space as the end point of the waveform data. Note that each point does not indicate a depth position.

  Then, in order to minimize the influence due to the limited amount of recorded data, a window function is applied to the time domain measurement signal (window processing is performed). Thereby, a continuous waveform without a rapid transition is obtained.

  In order to perform frequency analysis (FFT processing) on the A-line data, and to smooth the shape of the spectrum after the FFT processing, zero suppression is performed on the A-line data of 1152 points and 2048 points. Data. That is, 896 points are added to A line data of 1152 points, and the amplitude of the waveform at each added point is treated as 0.

  Then, 1024 frequency components are obtained by performing frequency analysis (FFT processing) on the continuous waveform of 2048 points. As a result of frequency analysis, it is found that a reflector or scatterer exists at a shallow position when a low frequency component is included in the waveform data, and a deep position when a high frequency component is included in the waveform data. .

  When the Y-direction galvanometer mirror 33Y has a predetermined rotation angle, the axis of the X-direction galvanometer mirror 33X is slightly rotated to shift the laser irradiation position in the lateral direction (X-axis direction) along the B line. Get line data. This is repeated the same number of times as a predetermined number of points (for example, 128 points) for the B line, and a three-dimensional slice image (A, B line data) is acquired.

  Here, the stereoscopic slice image can be generated by converting the 1024 amplitude intensities of the A line into luminance values for 1024 pixels. When the luminance value is expressed by 12 bits, for example, it is a numerical value of 0 to 4095, and any one of 0 to 4095 may be assigned to 1024 amplitude intensities.

  Further, the axis of the Y-direction galvanometer mirror 33Y is slightly rotated, the laser irradiation position is shifted in the vertical direction (Y-axis direction) along the V line, and slice images (A and B line data) are acquired. Go. This is repeated the same number of times as a predetermined number of points (for example, 128 points) on the V line, and solid data is obtained.

  As a predetermined number of points for the B line and the V line, for example, 128 points can be selected during preview, and 200 points, 300 points, and 400 points can be selected during measurement.

<3-4. On-face image generation processing>
Here, the on-face image generation processing will be described with reference to FIG.
Since each process of step S11-S15 is the same as each process of step S1-S5, description is abbreviate | omitted. Subsequently, the on-face image generation unit 151 of the image processing unit 150 adds the A line data (step S16). Here, as a result of FFT processing of the A line data, for example, when 1024 frequency components are obtained, a sum total of all 1024 frequency components is obtained.

  Then, the on-face image generation means 151 averages the sum of the A line data (step S17). Here, for example, when 1024 frequency components are obtained, the sum of A line data is divided by 1024 to obtain an average value. The averaging process of the frequency components in steps S16 and S17 is performed on an image (B × V line data) of a two-dimensional plane formed by the width direction (B line) of the sample S and the depth direction (V line) of the sample S. This corresponds to a process for obtaining one pixel value (see FIGS. 5A and 5B).

  Then, the on-face image generation means 151 determines whether or not the frequency component averaging processing has been completed for the B × V line data (step S18). If the processing has not been completed for the B × V line data (step S18: No), the on-face image generation unit 151 returns to step S16. On the other hand, when the processing is completed for the B × V line data (step S18: Yes), the on-face image generation unit 151 ends the process. For example, during preview, an on-face image with a resolution of 128 × 128 pixels is generated. Further, for example, when measuring 400 × 400, an on-face image having a resolution of 400 × 400 pixels is generated.

<3-5. Specific example of image processing timing>
Here, a specific example of image processing timing will be described with reference to FIG.
FIG. 8 is an example of a timing chart of image processing by the OCT control apparatus 100 according to the embodiment of the present invention.
FIG. 8A shows a scanning trigger (trigger: see FIG. 2) output from the light source 11.
FIG. 8B shows a start trigger (analog output) output from the DA conversion circuit 52, and has the same pulse waveform as that in FIG.
FIG. 8C shows the analog output voltage in the X direction output from the galvano mirror control circuit 53 to the X direction galvano mirror 33X.
FIG. 8D shows the analog output voltage in the Y direction output from the galvano mirror control circuit 53 to the Y direction galvano mirror 33Y.
FIG. 8E shows a clock (ck: see FIG. 2) output from the light source 11 for generating an OCT image.

  In this example, the sweep speed of the light source 11 is 50 kHz, and in synchronization with this, slight movement (rotation) and stop of the axis of the X-direction galvanometer mirror 33X are repeatedly performed at 50 kHz (pulse period 20 us). did. Note that us represents microseconds.

Preview or measurement is started at time S shown in FIG.
Waiting for a period of 15 pulses after the start, stereoscopic scanning starts at the time A shown in FIG. 8A, and one volume stereoscopic scanning ends at the time B shown in FIG. 8A. To do. At the time of measurement, the measurement ends at time B. At the time of preview, the process is repeated after returning to the time A after the time B.

  As shown in FIG. 8C, the analog output voltage in the X direction is −Vx at the time of A, becomes + Vx at the time of the 158th pulse from the time of A (mirror outward path), and then the 30th pulse. -Vx again at the time of (mirror return path). Thereafter, the processing is repeated until the one-dimensional stereoscopic scanning is completed.

  158 pulses shown in FIG. 8C correspond to 128 points on the B line. The reason why 158 points of data are acquired by 30 points more than the required 128 points is as follows. That is, since the amount of change in position at both ends where the galvano mirror 33 is at the maximum swing angle is very small, the data at 15 points at both ends cannot be put to practical use.

  Note that when measuring 200 points on the B line, it becomes + Vx at the time of the 230th pulse, at time of the 330th pulse when measuring 300 points, and at the time of the 430th pulse when measuring 400 points.

  Also, the reason why the mirror return path is moved in a shorter time than the mirror return path is because data on the mirror return path is not used. At this time, the operating speed of the galvanometer mirror 33 is limited (for example, a maximum of 100 Hz for oscillating ± 30 °), and therefore it is necessary to return the galvanometer mirror 33 at such a speed as not to break.

  As shown in FIG. 8D, the analog output voltage in the Y direction is −Vy from the time A to the time of the 158th pulse, and slightly changes at the 159th pulse (after the B line scan). Similarly, it slightly changes after the B-line scan, and becomes + Vy (mirror forward) at a predetermined time before the time when the one-dimensional stereoscopic scan is finished (30 pulses before time B), and then again at the time of the 30th pulse. -Vy (mirror return).

  As shown in FIG. 8E, in order to generate an image, data is sampled at 50 kHz (pulse period 20 us) from time A to time B. Then, for example, a slice image of the first frame is generated in a 128-pulse period in the mirror forward path (158 pulse period) from time A (imaging (first frame)). As described above, the acquired data for the period of 15 pulses before and after is not used. Similarly, a slice image of each frame is generated when scanning the B line. In this example, a 128-frame slice image is generated as V-line data.

<3-6. Online processing flow>
Here, the flow of the above-described online processing will be described with reference to FIGS. 9 and 10 (refer to FIGS. 3 and 12 to 15 as appropriate). First, when the power is turned on and the OCT apparatus 1 is activated, the OCT control apparatus 100 displays a main menu as a start page on the display device 54 (step S21). In the example illustrated in FIG. 12, various buttons such as a “start imaging” button and a “patient data browsing” button are displayed as buttons on the GUI screen.

  Here, when the user clicks the “start imaging” button with the mouse that is the input device M (step S22), the OCT control device 100 starts online processing, and displays a patient as shown in FIG. An information input screen is displayed (step S23). When the user inputs personal information such as the patient's name (step S24: Yes), necessary information is input for each item displayed on the screen (step S25), and the button is operated to proceed to the next step. Is performed (step S26). When the user's personal information 122 is confirmed and registered in the patient file 121 (see FIG. 3), when the “OK” button is clicked, the OCT control device 100 displays the online information as shown in FIG. A display screen is displayed (step S27). When the “Cancel” button is clicked on the patient information input screen, the screen returns to the main menu.

  Various information such as patient personal information is displayed on the left side of the upper part of the online screen shown in FIG. On the right side of the upper part of the online screen, “Map”, “Preview”, “Measure”, “400 × 400”, “ZeroAdj”, “Save”, “Setting”, “Exit”, etc. are arranged as operation buttons. Has been. These functions will be described later.

  When the user clicks the “Map” button on the online display screen (step S28), the OCT control apparatus 100 displays a “dental and tooth number” window on the online screen shown in FIG. 14 (step S29). .

  When the user clicks on a tooth from the dental arch in the window (step S30), the OCT control apparatus 100 highlights the tooth number in association with the tooth list in the window (step S30). S31).

  Here, the user performs a button operation to proceed to the next step (step S32). When the user clicks an “OK” button to photograph the input tooth, the OCT control device 100 displays an examination (online) screen as shown in FIG. 15, for example, on the display device 54 (step S33). Details of this online display screen will be described later. If the “Cancel” button is clicked in the “Dental and tooth number” window of the online screen, the process returns to step S27 to display the online screen.

  On the inspection (online) screen shown in FIG. 15, for example, when the user clicks a “ZeroAdj” button (step S34), zero point correction can be performed. Zero point correction is calibration before data recording, and indicates a process of measuring noise or the like of the optical system as background data by closing the shutter 31 (see FIG. 2) of the diagnostic probe unit 30. Thereby, the OCT image generation means 152 reduces the influence of noise by subtracting the background data from the recorded data at the time of data scanning.

  On the examination (online) screen shown in FIG. 15, for example, when the user clicks the “Preview” button (step S <b> 35), a preview instruction can be input to the second imaging control unit 142. The second shooting control unit 142 performs shooting in the preview mode (step S36: “Preview” shooting).

  On the examination (online) screen shown in FIG. 15, for example, when the user clicks the “Measure” button (step S 37), the preview instruction is canceled and the measurement instruction is input to the first imaging control unit 141. The first imaging control means 141 performs the actual imaging in the resolution measurement mode set at this time (step S38: “Measure” imaging).

  After photographing, on the inspection (online) screen shown in FIG. 15, the user performs a button operation to proceed to the next step (step S39). When re-imaging is desired, for example, when the “ZeroAdj” button is clicked, the OCT control apparatus 100 performs processing corresponding to step S34. Further, for example, when the “Preview” button or the “Measure” button is clicked, the OCT control apparatus 100 performs the processing of Step S36 and Step S38 as processing corresponding to Step S35 and Step S37. Further, when the image information 123 acquired by the main imaging is stored in the patient file 121 (see FIG. 3), the user clicks the “Save” button. Thereby, the image information 123 can be linked to the corresponding patient file 121 (see FIG. 3).

  When the user clicks the “Exit” button subsequent to the “Save” button after the main photographing (Step S38) (Step S40), the patient information input screen shown in FIG. 13 is displayed again (Step S41). At this time, if the user wants to see the main menu, the user clicks the “Cancel” button (step S42: Yes).

  In step S41, if the user wants to take an image of the next patient (step S42: No), the process returns to step S23 described above to input personal information of the next patient. When the patient information input screen shown in FIG. 13 is displayed (step S23), the user clicks the “Cancel” button without entering the personal information of the next patient (step S24: Yes). back to menu. Further, when the user clicks the “Exit” button without pressing the “Save” button in the button operation (Step S39) after the end of the main photographing (Step S38), the main menu is displayed again (Step S21). When the “EXIT” button is clicked in the main menu shown in FIG. 12, the OCT control apparatus 100 ends the process.

  As described above, when the measurement instruction is input to the imaging control unit 140 with the foot controller 80 instead of operating the “Preview” button and the “Measure” button displayed on the inspection (online) screen, the main imaging (step S38) is performed. ) After the completion, although not shown in the figure, a message for inquiring to save the photographed image information, a “Yes” button, and a “No” button are displayed on the display device 54. When the user depresses the pedal of the foot controller 80 by one step, either “Yes” or “No” is selected. Here, for example, when “Yes” is selected, when the user depresses the pedal of the foot controller 80 by another step, that is, a total of two steps, the image information storage instruction is fixed.

  If the user first depresses the pedal by one step and releases his / her foot when “Yes” is selected, the pedal returns to the original position and the current selection “Yes” is not confirmed. When the user depresses the pedal of the foot controller 80 again by one step, the display is changed to “No”. Hereinafter, similarly, “Yes” and “No” before confirmation can be switched.

<3-7. Offline processing flow>
Here, the flow of the above-described offline processing will be described with reference to FIG. 11 (refer to FIG. 3, FIG. 12 and FIGS. 15 to 19 as appropriate). First, the OCT control device 100 displays the main menu shown in FIG. 12 as a start page on the display device 54 (step S51).

  Here, when the user clicks the “browse patient data” button (step S52), the OCT control device 100 starts offline processing and causes the display device 54 to display, for example, a patient search screen as shown in FIG. Step S53). If the “Cancel” button is clicked on the patient search screen (step S54: Yes), the screen returns to the main menu. Then, the user inputs the patient ID or the patient's name as a search condition (Step S55) without canceling (Step S54: No), and clicks the “Search” button (Step S56). The result is displayed in the patient list on the patient search screen (step S57).

  Subsequently, the user performs a button operation to proceed to the next step (step S58). When the user clicks an “OK” button to display a patient file for a patient as a search result, the OCT control device 100 causes the display device 54 to display a file selection screen as shown in FIG. 17, for example (step S59). In step S58, when the “Cancel” button is clicked, the screen returns to the main menu. When the “EXIT” button is clicked in the main menu shown in FIG. 12, the OCT control apparatus 100 ends the process.

  If the user clicks the “Exit” button while the file selection screen shown in FIG. 17 is being displayed (step S60: Yes), the OCT control device 100 returns to step S53 to display the patient search screen. The user does not click the “Exit” button on the file selection screen (step S60: No), but selects the patient file from the table or the dental arch by imaging date and time (step S61), and clicks the “Select” button. Then (step S62), the OCT control apparatus 100 causes the display device 54 to display an offline display screen as shown in FIG. 19, for example (step S63). Details of this offline display screen will be described later. When the user clicks the “Exit” button on the offline display screen (step S64), the OCT control device 100 returns to step S59 to display the file selection screen.

[4. Screen display example of display device]
Here, the inspection (online) screen shown in FIG. 15 and the offline display screen shown in FIG. 19 will be described.
<Inspection (online) screen>
On this inspection (online) screen, a 3D screen arranged on the left side of FIG. 15, an on-face screen arranged on the lower center side of FIG. 15, and an OCT screen arranged on the upper upper side of FIG. 15 are displayed as image information. ing.

  In the example illustrated in FIG. 15, a virtual space of a cube is assumed that matches the position of the sample S (molar tooth) positioned at the nozzle tip of the diagnostic probe unit 30. For example, on an on-face screen, each surface of the cube is represented by an S-plane (on-face image sample S surface: upper surface), an A-plane (front surface viewed from the on-face image sample S-plane), and a P-plane (on-face image sample S). Rear surface viewed from the surface), R surface (right side when looking forward from the sample S surface of the Onface image), L surface (left side when looking forward from the Sample S surface of the Onface image), I surface ( The opposite surface of the sample S surface of the on-face image: the lower surface).

  The 3D screen designates the A, P, S, I, R, and L planes of “Camera Angle” on the right side of the online screen, thereby displaying a stereoscopic image viewed from a desired plane in real time. The illustrated example is a front left image of the sample S viewed from the S plane (sample S plane of the on-face image).

  The on-face screen displays an on-face image in which information on the surface of the sample S viewed from the S-plane (sample S-plane of the on-face image) and information on the depth direction of the sample S are combined. On-face images also show internal information that is not originally visible on the outer surface.

  The OCT screen is a plane parallel to the A plane (the front surface viewed from the sample S plane of the Onface image), and is an OCT image of a cut surface (tomographic plane) cut by a line 1502 indicated by a horizontal line arranged in the Onface image. Is displayed. In the example of FIG. 15, an image of a tomographic plane in the direction of viewing the P plane from the A plane is displayed as an OCT image. Conversely, an image of a tomographic plane in the direction of viewing the A plane from the P plane may be displayed as an OCT image. The line 1502 can be moved by an operation on a GUI (graphical user interface). Specifically, the slider 1501 displayed as a bar between the Onface screen and the OCT screen can be moved by dragging and dropping it with, for example, a mouse (input device M). That is, the slider 1501 is moved by moving the mouse while pressing the mouse button, and the operation of the slider 1502 is terminated by releasing the mouse button. When the mouse button is released, The OCT image on the tomographic plane corresponding to the position of the line on the on-face screen is displayed on the OCT screen. Alternatively, the line 1502 itself can be moved by dragging and dropping with a mouse, and a tomographic plane corresponding to the position of the line can be displayed. Since the on-face image is a monochrome image, it is preferable to display the lines on the on-face screen in red or the like.

  “Preview” indicates a button for inputting a preview instruction. When this button is pressed, the respective images are displayed in real time on the 3D screen, the on-face screen, and the OCT screen. For example, the 3D image is updated approximately every 1 second. If the nozzle tip of the diagnostic probe unit 30 is moved, the image information (preview image) that follows it can be acquired. Note that the preview image is not premised on storage.

  “Measure” indicates a button for inputting a measurement instruction. When the “Measure” button is pressed during the preview, the preview instruction is canceled and the main shooting is started. The shooting is automatically completed at the shooting time corresponding to the resolution selected at that time. The main photographing is photographing premised on preservation, and is performed with the sample S fixed. Here, “fixed” means that the nozzle tip of the diagnostic probe unit 30 is brought into contact with the sample S. At this time, for example, the patient may stay still. In the case of a resolution of “400 × 400”, the main shooting is completed in about 3 seconds, and when the resolution is lower than that, the shooting is completed in less than 3 seconds.

  “400 × 400” indicates a button for inputting a resolution. This button is “128 × 128” during preview. When the button is pressed before measurement, one of resolutions “200 × 200”, “300 × 300”, and “400 × 400” can be selected from the pull-down menu.

  “Setting” indicates a button for inputting a range to be scanned by the galvanometer mirror 33. When this button is pressed, one of three areas S, M, and L can be selected from the pull-down menu. Based on the operation data input at this time, the scanning area selection control unit 143 (see FIG. 3) determines a range to be scanned by the galvanometer mirror 33.

On the right side of the online screen, a slider for adjusting the settings of the 3D screen, all screen displays, images displayed on the A screen, and the like is displayed as a bar.
“Window Width” is a bar for determining the adjustment range of contrast.
“Window Level” is a bar for determining the median value of Window Width.
“Gamma” is a bar for emphasizing weak signals so that the contrast can be adjusted. In the example shown in the figure, a state in which “3D screen” is designated and adjustment is performed using the lower slider is shown.

<Offline display screen>
Here, a specific example of the offline display screen will be described with reference to FIG.
The offline display screen displays a 3D screen rendered from saved data on the left side of FIG. 19 as image information.
The OCT screen arranged at the upper left center of FIG. 19 shows a tomographic image cut by a cross section parallel to the S plane (sample S plane of the on-face image). By moving the slider displayed on the lower side of the OCT screen, an image parallel to the scan plane corresponding to any depth position of the A line (1024-point FFT) (any of 1024 images) Can be displayed.
An OCT screen arranged at the lower left center of FIG. 19 shows a tomographic image cut by a cross section parallel to the A plane. By moving a slider displayed as a bar on the lower side of the OCT screen, a slice image (A, B line data) corresponding to any position of the V line (400 points) can be displayed.
The OCT screen arranged at the upper right corner of FIG. 19 shows a tomographic image cut by a cross section parallel to the L plane. By moving the slider displayed on the lower side of the OCT screen, a slice image (A, V line data) corresponding to any position of the B line (400 points) can be displayed.
The on-face screen arranged in the lower right center of FIG. 19 displays an on-face image viewed from the S-plane (sample surface S of the on-face image).

Various information such as patient personal information is displayed on the left side of the upper part of the offline display screen.
In the center of the upper part of the online display screen, the shooting date and the shooting site are displayed.
On the right side of the upper part of the offline display screen, “Export”, “EXIT” and the like are arranged as operation buttons. “Export” indicates a button for converting and outputting image data.

  According to the present embodiment, the OCT control device 100 causes the display device 54 to display the “dental and tooth number” window on the display device 54 by the input support processing unit 161, and the tooth is displayed from the dental arch displayed in the window. When is selected, the tooth number of the tooth can be recorded and associated with the tooth list displayed in the window. As a result, it is possible to save the trouble of inputting the tooth number and symbol and to improve the operability.

  Further, according to the present embodiment, the OCT control apparatus 100 displays the patient file list being displayed when a tooth is selected from the dental arch side on the file selection screen by the imaging region confirmation display processing unit 162. On the other hand, if the tooth number is specified from the selection of the patient file list, the tooth is extracted from the dental arch and displayed. Accordingly, the user can intuitively understand the correspondence between the image information associated with the patient file information created by photographing and the tooth number of the tooth in the dental arch displayed on the screen. .

  As mentioned above, although embodiment of this invention was described, this invention is not limited to this, It can implement in the range which does not change the meaning. For example, in the preview mode, the OCT control apparatus 100 starts imaging when it is determined that an input of a preview instruction is received from the outside, and ends imaging when it is determined that an input of a measurement instruction is received. Of course, a preview instruction cancel instruction may be issued separately from the measurement instruction input.

Further, the present invention is not limited to the performance of the laser used in the light source 11 as a highly coherent one having a coherence distance (coherent length) of 10 mm or more.
Moreover, although this embodiment demonstrated using SS-OCT system, you may use SD-OCT and TD-OCT.
4B, the nozzle tip shown in FIG. 4B is preferably used when the sample S is an anterior tooth. When the sample S is a molar, a member capable of reflecting laser light at a right angle is used. It is preferable to attach to the nozzle tip.

1,1A OCT system (dental optical coherence tomographic image generator)
10 Optical unit (optical unit)
DESCRIPTION OF SYMBOLS 11 Light source 12 Coupler 13 Sample arm 14 Circulator 15 Polarization controller 16 Coupler 17 Reference arm 18 Circulator 19 Collimator lens 20 Condensing lens 21 Reference mirror 22 Polarization controller 23 Detector (detector)
30 Diagnostic probe section (probe)
31 Shutter 32 Collimator lens 33 Galvano mirror (scanning mechanism)
33X X direction galvanometer mirror 33Y Y direction galvanometer mirror 34 Condensing lens 50 Control unit (control unit)
51 AD conversion circuit 52 DA conversion circuit 53 Galvano mirror control circuit 54 Display device 60 Cable 70 Single joint arm 70A Articulated arm 80 Foot controller 100 OCT control device 110 Input / output means 120 Storage means 121 Patient file 122 Patient personal information 123 Image information DESCRIPTION OF SYMBOLS 130 Calculation means 140 Imaging | photography control means 141 1st imaging | photography control means 142 2nd imaging | photography control means 143 Scanning area selection control means 150 Image processing means 151 On-face image generation means 152 OCT image generation means 153 Rendering means 154 Tomographic position line generation means 160 File Creation processing means 161 Input support processing means 162 Imaging region confirmation display processing means M Input device S Sample (subject)

Claims (6)

An optical unit that includes a light source that periodically irradiates a subject with laser light and a detector that detects internal information of the subject, and a scanning mechanism that two-dimensionally scans the laser light. A probe that guides light reflected by the subject to the optical unit and a probe that guides the light reflected by the subject to the optical unit, and controls the scanning mechanism in synchronization with the laser light to perform imaging and convert the detection signal of the detector from the data A control device that performs control to generate an optical coherence tomographic image of a subject and a control unit that includes a display device that displays the optical coherence tomographic image, the control device of a dental optical coherence tomographic image generation device comprising:
Shooting control means for shooting in a predetermined shooting mode based on an external input;
Image processing means for image processing the detection signal acquired by photographing;
File creation processing means for creating patient file information for file management of personal information for each patient and captured image information of the subject;
Tooth position information used in common for each patient in which the tooth number according to a predetermined dental formula and the positions of the upper and lower dental arches are associated in advance, and storage means for storing the patient file information,
The file creation processing means
An image display field for displaying an image of a dental arch before imaging, and a display field for a tooth list table having a tooth number item and an imaging target tooth number item for all teeth on a single screen. When the imaging part display screen is displayed on the display device and a predetermined tooth in the displayed image of the dental arch is selected, the tooth number of the tooth is specified based on the tooth position information, and the patient An input support processing unit that performs processing for associating the identified tooth number with the photographing target tooth number in the tooth list, in association with file information and photographing date and time,
Displayed on the display device is a file selection screen for each patient that includes an image display field for displaying an image of a dental arch and a display field for displaying a patient file list for a specified patient after imaging. When a predetermined tooth in the displayed image of the dental arch is selected, the tooth number of the tooth is specified based on the tooth position information, and the corresponding patient file in the patient file list is extracted When a predetermined patient file in the patient file list is selected, the tooth of the tooth number is identified in the dental arch image based on the tooth position information, An imaging region confirmation display processing means for performing processing for extracting and displaying the identified tooth;
A control apparatus for a dental optical coherence tomographic image generation apparatus, comprising: The imaging region confirmation display processing means includes
After imaging, when a predetermined tooth or tooth number is selected on the file selection screen displayed on the display device, the captured image information of the selected tooth or tooth number is obtained based on the patient file information. The control apparatus for a dental optical coherence tomographic image generation apparatus according to claim 1, further comprising a process of displaying the file selection screen together. The photographing control means includes
Shooting is started when it is determined that the scanning mechanism has received an input of a measurement instruction for scanning the shooting target range of the subject at a predetermined pitch in order to measure internal information of the subject, and a shooting time corresponding to the predetermined pitch First shooting control means for ending shooting at;
When it is determined that an input of a preview instruction for allowing the scanning mechanism to scan the imaging target range at a pitch coarser than the predetermined pitch is received, and an input of an instruction for canceling the preview instruction is received. Second shooting control means for ending shooting at the same time;
The control apparatus for a dental optical coherence tomographic image generation apparatus according to claim 1, comprising: The image processing means includes
As a two-dimensional image of the scan plane in the direction perpendicular to the optical axis of the subject, an image in which information on the surface of the subject irradiated with the laser light and information on the direction along the optical axis in the subject are combined. An on-face image generation means for generating an on-face image;
A tomographic position line generation unit that draws and superimposes the tomographic position of the optical coherence tomographic image on the line on the on-face image displayed on the display device;
An instruction to select and move the line of the tomographic position displayed on the display device is received, and the optical coherence tomographic image is generated from data obtained by converting the detection signal of the detector based on the information of the selected and moved line Optical coherence tomographic image generating means for
The control apparatus of the dental optical coherence tomographic image generation apparatus according to any one of claims 1 to 3, further comprising: An optical unit that includes a light source that periodically irradiates a subject with laser light and a detector that detects internal information of the subject, and a scanning mechanism that two-dimensionally scans the laser light. A probe that guides light reflected by the subject to the optical unit and a probe that guides the light reflected by the subject to the optical unit, and controls the scanning mechanism in synchronization with the laser light to perform imaging and convert the detection signal of the detector from the data A control method for a dental optical coherence tomographic image generation apparatus comprising: a control device that performs control to generate an optical coherence tomographic image of a subject; and a control unit that includes a display device that displays the optical coherence tomographic image,
The controller is
Tooth commonly used for each patient in which patient file information for file management of patient-specific personal information and photographed image information of the subject, tooth numbers according to a predetermined tooth type, and positions of upper and lower dental arches are associated in advance Storage means for storing position information;
An image display field for displaying an image of a dental arch before imaging, and a display field for a tooth list table having a tooth number item and an imaging target tooth number item for all teeth on a single screen. When the imaging part display screen is displayed on the display device and a predetermined tooth in the displayed image of the dental arch is selected, the tooth number of the tooth is specified based on the tooth position information, and the patient A step of performing processing for associating the specified tooth number with the photographing target tooth number in the tooth list, associating it with the file information and the photographing date and time,
Displayed on the display device is a file selection screen for each patient that includes an image display field for displaying an image of a dental arch and a display field for displaying a patient file list for a specified patient after imaging. When a predetermined tooth in the displayed image of the dental arch is selected, the tooth number of the tooth is specified based on the tooth position information, and the corresponding patient file in the patient file list is extracted A process of performing display, and
After imaging, when a predetermined patient file in the patient file list is selected on the file selection screen displayed on the display device, the tooth in the dental arch image is selected based on the tooth position information. Identifying the tooth of the number, performing a process of extracting and displaying the identified tooth;
And a control method for a dental optical coherence tomographic image generation apparatus.   A dental optical coherence tomographic image generation apparatus control program for causing a computer to function as each means of the control apparatus for a dental optical coherence tomographic image generation apparatus according to any one of claims 1 to 4.

Images