JP6381123B2 - Optical scanning observation system - Google Patents

Description

  The present invention relates to an optical scanning observation system, and more particularly to an optical scanning observation system that acquires an image by scanning a subject.

  In endoscopes in the medical field, various techniques have been proposed for reducing the diameter of an insertion portion that is inserted into a body cavity of a subject in order to reduce the burden on the subject. As an example of such a technique, a scanning endoscope that does not include a solid-state imaging device in a portion corresponding to the above-described insertion portion, and a system that includes the scanning endoscope are known. ing.

  Specifically, a system including a scanning endoscope, for example, moves a subject along a predetermined scanning path by swinging a tip of an optical fiber for illumination that guides light emitted from a light source unit. Two-dimensional scanning is performed, and return light from the subject is received by a light receiving optical fiber, and an image of the subject is generated based on the return light received by the light receiving optical fiber.

  Also, in a system including a scanning endoscope, for example, due to an error between a scanning path when an object is actually scanned and an ideal scanning path, the image obtained by scanning the object is distorted. May occur. As an example of a technique for calibrating such image distortion, a calibration method disclosed in Patent Document 1 is known.

  Specifically, Patent Document 1 discloses a histogram showing a light amount distribution of scanning light obtained when scanning is actually performed with a predetermined scanning path, and an ideal when scanning is performed with the predetermined scanning path. A correction value used for calibration of image distortion obtained by scanning the subject is calculated on the basis of a scanning error amount obtained by comparing a master histogram indicating a correct light amount distribution, and the calculated correction value is A configuration in which data is stored in a sub-memory provided in the confocal probe is disclosed.

  However, according to the configuration disclosed in Patent Document 1, as the amount of correction value data stored in the sub-memory increases, it takes longer to complete the reading of the correction value data. There is a problem. As a result, according to the configuration disclosed in Patent Document 1, for example, as the scanning range by the confocal probe is expanded, the time required from when the system is turned on until the image is displayed becomes longer. There is a problem corresponding to the above-mentioned problems.

  The present invention has been made in view of the above-described circumstances, and an object thereof is to provide an optical scanning observation system capable of shortening the time required from when the power is turned on until an image is displayed as much as possible.

  An optical scanning observation system according to an aspect of the present invention includes an endoscope configured to scan a subject with illumination light emitted from a light source unit and receive return light, and a main body to which the endoscope can be connected A first storage that is provided in the apparatus and stores reference scanning position information that is information indicating an irradiation position of the illumination light that is used as a reference when the illumination light is irradiated and the subject is scanned along a predetermined scanning path. An irradiation position of the illumination light when the illumination light is irradiated using the endoscope and the subject is actually scanned along the predetermined scanning path, and the reference A second storage unit storing differential scanning position information, which is information indicating a difference value between the irradiation position of the illumination light included in the scanning position information, and the first storage unit. The reference scanning position information read from A third storage unit storing correction scanning position information acquired as a result of processing based on the differential scanning position information read from the storage unit, and the correction scanning read from the third storage unit An image generation unit configured to generate an image according to the return light received by the endoscope connected to the main body device using the scanning position information and output the image to a display device. .

  According to the optical scanning observation system of the present invention, the time required from when the power is turned on until an image is displayed can be shortened as much as possible.

The figure which shows the structure of the principal part of the optical scanning type observation system which concerns on an Example. Sectional drawing for demonstrating the structure of an actuator part. The figure which shows an example of the signal waveform of the drive signal supplied to an actuator part. The figure which shows an example of the spiral scanning path | route from the center point A to the outermost point B. FIG. The figure which shows an example of the spiral scanning path | route from the outermost point B to the center point A. FIG. The figure which shows typically the relationship between coordinate position data MV and TV, and difference data DV.

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

  1 to 6 relate to an embodiment of the present invention. FIG. 1 is a diagram illustrating a configuration of a main part of an optical scanning observation system according to an embodiment.

  For example, as shown in FIG. 1, the optical scanning observation system 1 includes a scanning endoscope 2 that is inserted into a body cavity of a subject, a main body device 3 that can connect the endoscope 2, and a main body A display device 4 connected to the device 3 and an input device 5 capable of inputting information and giving instructions to the main device 3 are configured.

  The endoscope 2 includes an insertion portion 11 formed with an elongated shape that can be inserted into a body cavity of a subject.

  A connector portion 61 for detachably connecting the endoscope 2 to the connector receiving portion 62 of the main body device 3 is provided at the proximal end portion of the insertion portion 11.

  Although not shown in the drawings, an electrical connector device for electrically connecting the endoscope 2 and the main body device 3 is provided inside the connector portion 61 and the connector receiving portion 62. Although not shown, an optical connector device for optically connecting the endoscope 2 and the main body device 3 is provided inside the connector portion 61 and the connector receiving portion 62.

  An illumination fiber 12 that is an optical fiber that guides the illumination light supplied from the light source unit 21 of the main body device 3 to the illumination optical system 14 in a portion from the proximal end portion to the distal end portion inside the insertion portion 11, and A light receiving fiber 13 including one or more optical fibers for receiving return light from the subject and guiding it to the detection unit 23 of the main body device 3 is inserted therethrough.

  The incident end including the light incident surface of the illumination fiber 12 is disposed in a multiplexer 32 provided inside the main body device 3. Further, the emission end portion including the light emission surface of the illumination fiber 12 is disposed in the vicinity of the light incident surface of the lens 14 a provided at the distal end portion of the insertion portion 11.

  The incident end including the light incident surface of the light receiving fiber 13 is fixedly disposed around the light emitting surface of the lens 14 b at the distal end surface of the distal end portion of the insertion portion 11. Further, the emission end portion including the light emission surface of the light receiving fiber 13 is arranged in a duplexer 36 provided inside the main body device 3.

  The illumination optical system 14 includes a lens 14a on which illumination light having passed through the light emission surface of the illumination fiber 12 is incident, and a lens 14b that emits illumination light having passed through the lens 14a to a subject.

  An actuator unit 15 that is driven based on a drive signal supplied from the driver unit 22 of the main unit 3 is provided in the middle of the illumination fiber 12 on the distal end side of the insertion unit 11.

  The illumination fiber 12 and the actuator unit 15 are arranged so as to have the positional relationship shown in FIG. 2, for example, in a cross section perpendicular to the longitudinal axis direction of the insertion unit 11. FIG. 2 is a cross-sectional view for explaining the configuration of the actuator unit.

  As shown in FIG. 2, a ferrule 41 as a joining member is disposed between the illumination fiber 12 and the actuator unit 15. Specifically, the ferrule 41 is made of, for example, zirconia (ceramic) or nickel.

  As shown in FIG. 2, the ferrule 41 is formed as a quadrangular prism, and side surfaces 42 a and 42 c that are perpendicular to the X-axis direction, which is the first axial direction orthogonal to the longitudinal axis direction of the insertion portion 11, Side surfaces 42b and 42d perpendicular to the Y-axis direction, which is the second axial direction perpendicular to the longitudinal axis direction of the insertion portion 11, are included. The illumination fiber 12 is fixedly arranged at the center of the ferrule 41. The ferrule 41 may be formed as a shape other than the quadrangular column as long as it has a column shape.

  As shown in FIG. 2, the actuator section 15 includes a piezoelectric element 15a disposed along the side surface 42a, a piezoelectric element 15b disposed along the side surface 42b, and a piezoelectric element 15c disposed along the side surface 42c. , And a piezoelectric element 15d disposed along the side surface 42d.

  The piezoelectric elements 15 a to 15 d have polarization directions that are individually set in advance, and are configured to expand and contract in accordance with a drive signal supplied from the main body device 3.

  That is, the endoscope 2 is configured to scan the subject with illumination light emitted from the light source unit 21 of the main body device 3 and to receive the return light from the subject through the light receiving fiber 13.

  Inside the insertion unit 11, a nonvolatile memory 16 is provided for storing differential scanning position data (described later) unique to each endoscope 2. The differential scanning position data stored in the memory 16 is obtained when the connector portion 61 of the endoscope 2 and the connector receiving portion 62 of the main body device 3 are connected and the power of the main body device 3 is turned on. Read by the controller 25 of the main unit 3. The differential scanning position data is assumed to be stored in the memory 16 at an arbitrary timing before the user uses the endoscope 2 for the first time, such as when the endoscope 2 is manufactured.

  The main device 3 includes a light source unit 21, a driver unit 22, a detection unit 23, a nonvolatile memory 24a, a volatile memory 24b, and a controller 25.

  The light source unit 21 includes a light source 31a, a light source 31b, a light source 31c, and a multiplexer 32.

  The light source 31a includes a laser light source, for example, and is configured to emit red wavelength band light (hereinafter also referred to as R light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.

  The light source 31b includes, for example, a laser light source, and is configured to emit green wavelength band light (hereinafter also referred to as G light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.

  The light source 31c includes, for example, a laser light source, and is configured to emit light in a blue wavelength band (hereinafter also referred to as B light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.

  The multiplexer 32 multiplexes the R light emitted from the light source 31a, the G light emitted from the light source 31b, and the B light emitted from the light source 31c onto the light incident surface of the illumination fiber 12. It is configured to supply.

  The driver unit 22 includes a signal generator 33, D / A converters 34a and 34b, and an amplifier 35.

  Based on the control of the controller 25, the signal generator 33 is a predetermined drive signal as shown by a broken line in FIG. 3, for example, as a first drive signal for swinging the emission end of the illumination fiber 12 in the X-axis direction. A signal having a signal waveform obtained by performing the above modulation on a sine wave is generated and output to the D / A converter 34a. Further, the signal generator 33 is, for example, indicated by a one-dot chain line in FIG. 3 as a second drive signal for swinging the emission end of the illumination fiber 12 in the Y-axis direction based on the control of the controller 25. A signal having a signal waveform in which the phase of the first drive signal is shifted by 90 ° is generated and output to the D / A converter 34b. FIG. 3 is a diagram illustrating an example of a signal waveform of a drive signal supplied to the actuator unit.

  The D / A converter 34 a is configured to convert the digital first drive signal output from the signal generator 33 into an analog first drive signal and output the analog first drive signal to the amplifier 35.

  The D / A converter 34 b is configured to convert the digital second drive signal output from the signal generator 33 into an analog second drive signal and output the analog second drive signal to the amplifier 35.

  The amplifier 35 is configured to amplify the first and second drive signals output from the D / A converters 34 a and 34 b and output the amplified signals to the actuator unit 15.

  Here, for example, a first drive signal having a signal waveform as shown by a broken line in FIG. 3 is supplied to the piezoelectric elements 15a and 15c of the actuator unit 15, and a signal waveform as shown by a one-dot chain line in FIG. Is supplied to the piezoelectric elements 15b and 15d of the actuator unit 15, the emission end of the illumination fiber 12 is swung in a spiral shape, and the subject is responsive to such a swing. Are scanned by a spiral scanning path as shown in FIGS. FIG. 4 is a diagram illustrating an example of a spiral scanning path from the center point A to the outermost point B. FIG. FIG. 5 is a diagram illustrating an example of a spiral scanning path from the outermost point B to the center point A. FIG.

  Specifically, at time T1, illumination light is irradiated to a position corresponding to the center point A of the irradiation position of the illumination light on the surface of the subject. Thereafter, as the amplitudes of the first and second drive signals increase from time T1 to time T2, the irradiation position of the illumination light on the surface of the subject starts from the center point A and starts to the first spiral scanning path. When the time T2 is reached, the illumination light is irradiated to the outermost point B of the illumination light irradiation position on the surface of the subject. Then, as the amplitudes of the first and second drive signals decrease from time T2 to time T3, the irradiation position of the illumination light on the surface of the subject is scanned in the second spiral shape from the outermost point B to the inside. When it is displaced so as to draw a route and further reaches time T3, illumination light is applied to the center point A on the surface of the subject.

  That is, the actuator unit 15 is emitted to the subject through the emission end by swinging the emission end of the illumination fiber 12 based on the first and second drive signals supplied from the driver unit 22. The illumination light irradiation position can be displaced along the spiral scanning path shown in FIGS. 4 and 5.

  The detection unit 23 includes a duplexer 36, detectors 37a, 37b, and 37c, and A / D converters 38a, 38b, and 38c.

  The demultiplexer 36 includes a dichroic mirror and the like, and separates the return light emitted from the light emitting surface of the light receiving fiber 13 into light for each of R (red), G (green), and B (blue) color components. And it is comprised so that it may radiate | emit to the detectors 37a, 37b, and 37c.

  The detector 37a includes, for example, an avalanche photodiode and the like, detects the intensity of the R light output from the duplexer 36, generates an analog R signal corresponding to the detected intensity of the R light, and generates A It is configured to output to the / D converter 38a.

  The detector 37b includes, for example, an avalanche photodiode, detects the intensity of the G light output from the branching filter 36, generates an analog G signal corresponding to the detected intensity of the G light, and generates A It is configured to output to the / D converter 38b.

  The detector 37c includes, for example, an avalanche photodiode and the like, detects the intensity of the B light output from the demultiplexer 36, generates an analog B signal corresponding to the detected intensity of the B light, and generates A It is configured to output to the / D converter 38c.

  The A / D converter 38 a is configured to convert the analog R signal output from the detector 37 a into a digital R signal and output it to the controller 25.

  The A / D converter 38b is configured to convert the analog G signal output from the detector 37b into a digital G signal and output the digital G signal to the controller 25.

  The A / D converter 38 c is configured to convert the analog B signal output from the detector 37 c into a digital B signal and output it to the controller 25.

  In the memory 24a, for example, information including parameters such as a signal level, a frequency, and a phase difference for specifying the signal waveform in FIG. 3 is stored in advance as control information used when controlling the main unit 3. . Further, the memory 24a stores in advance reference scanning position data indicating the irradiation position of the illumination light that serves as a reference when the subject is scanned along the spiral scanning path.

  The reference scanning position data is, for example, coordinate position data indicating an ideal illumination light irradiation position in a spiral scanning path (first and second spiral scanning paths) as shown in FIGS. Is stored in advance in the memory 24a. According to the present embodiment, for example, coordinate positions obtained by actually scanning a light irradiation coordinate detection module (described later) along a spiral scanning path using a plurality of endoscopes connectable to the main body device 3. The average value or median value of the data may be stored in advance in the memory 24a as reference scanning position data. Specifically, for example, the endoscope 2 connected to the main body device 3 is selected from among a plurality of models defined according to the fiber diameter of the illumination fiber 12 and / or the sizes of the piezoelectric elements 15a to 15d. When it can be classified into one model, it can be obtained by actually scanning the light irradiation coordinate detection module with a spiral scanning path using a plurality of endoscopes belonging to the one model and connectable to the main unit 3. The average value or median value of the coordinate position data obtained may be stored in advance in the memory 24a as the reference scanning position data.

  The memory 24b stores correction scanning position data (described later) obtained as a result of processing by the arithmetic processing unit 25c. The correction scanning position data stored in the memory 24b is erased when the power of the main unit 3 is turned off.

  The controller 25 is configured by an integrated circuit such as an FPGA (Field Programmable Gate Array). Further, the controller 25 detects whether or not the insertion portion 11 is electrically connected to the main body device 3 by detecting the connection state of the connector portion 61 in the connector receiving portion 62 via a signal line or the like (not shown). It is configured to be able to. The controller 25 includes a light source control unit 25a, a scanning control unit 25b, an arithmetic processing unit 25c, and an image generation unit 25d.

  Based on the control information read from the memory 24a, the light source control unit 25a is configured to perform control for the light source unit 21 to cause the light sources 31a to 31c to emit light simultaneously, for example.

  Based on the control information read from the memory 24a, the scanning control unit 25b is configured to control the driver unit 22 to generate a drive signal having a signal waveform as shown in FIG. 3, for example. Yes.

  The arithmetic processing unit 25c is a difference stored in advance in the memory 16 when the connector unit 61 of the endoscope 2 and the connector receiving unit 62 of the main unit 3 are connected and the main unit 3 is powered on. The scanning position data and the reference scanning position data stored in advance in the memory 24a are respectively read. In addition, the arithmetic processing unit 25c acquires correction scanning position data by performing predetermined processing using the differential scanning position data read from the memory 16 and the reference scanning position data read from the memory 24a. The scanning position data for correction acquired as the processing result of the predetermined processing is configured to be stored in the memory 24b.

  The image generation unit 25d uses the correction scanning position data read from the memory 24b, maps the luminance value indicated by the digital signal output from the detection unit 23, generates an observation image for one frame, and generates the generated image. An observation image for one frame is sequentially output to the display device 4. The image generation unit 25d is configured to perform processing for displaying a predetermined character string or the like on the display device 4.

  Specifically, for example, the image generation unit 25d detects the most recent scanning path based on the signal waveform of the drive signal generated by the control of the scanning control unit 25b, and reads the correction scanning position data read from the memory 24b. The pixel position of the raster scan format corresponding to the irradiation position of the illumination light on the detected scanning path is specified, and the luminance value indicated by the digital signal output from the detection unit 23 is mapped to the specified pixel position. Thus, an observation image for one frame is generated, and the generated observation image for one frame is sequentially output to the display device 4.

  The display device 4 includes, for example, a monitor and is configured to display an observation image output from the main body device 3.

  The input device 5 includes, for example, a keyboard or a touch panel. The input device 5 may be configured as a separate device from the main body device 3 or may be configured as an interface integrated with the main body device 3.

  Next, the operation of the optical scanning observation system 1 having the configuration as described above will be described.

  First, a specific example of a method for acquiring differential scanning position data stored in the memory 16 will be described.

  For example, when manufacturing the endoscope 2, the factory worker connects each part of the optical scanning observation system 1, turns on the power, detects the light irradiation position, and uses it as coordinate position data MV (xm, ym). A light receiving surface of a light irradiation coordinate detection module (not shown) configured to output and a distal end surface of the endoscope 2 are arranged to face each other, and the coordinate position data MV (xm, ym) is an arithmetic processing unit A cable or the like (not shown) is wired so as to be input to 25c.

  Thereafter, the factory worker operates the predetermined switch of the input device 5 to instruct the controller 25 to start scanning with the endoscope 2. In response to such an instruction, the light receiving surface of the light irradiation coordinate detection module is scanned along a spiral scanning path, and the coordinate position data MV (xm, ym) obtained by the light irradiation coordinate detection module is calculated. The data is output to the processing unit 25c. That is, the coordinate position data MV (xm, ym) indicates the irradiation position of the illumination light when the light irradiation coordinate detection module is actually scanned with the spiral scanning path using the endoscope 2. Note that the coordinate position data MV (xm, ym) is, for example, the coordinate position of the orthogonal coordinate system when the center point A of the spiral scanning path shown in FIGS. 4 and 5 is set to the origin (0, 0). Shall be obtained as

  When the arithmetic processing unit 25c detects that there is no differential scanning position data to be read from the memory 16, the arithmetic processing unit 25c stores the coordinate position data MV (xm, ym) sequentially output from the light irradiation coordinate detection module and the memory 24a. A process for obtaining difference data DV (xm-xt, ym-yt) indicating a difference value from coordinate position data TV (xt, yt) included in the obtained reference scanning position data is performed (see FIG. 6). . FIG. 6 is a diagram schematically illustrating the relationship between the coordinate position data MV and TV and the difference data DV.

  Then, the arithmetic processing unit 25c repeatedly performs the above-described processing, whereby difference data DV (xm−xt) corresponding to each coordinate position data TV (xt, yt) included in the reference scanning position data stored in the memory 24a. , Ym−yt), and the obtained difference data DV (xm−xt, ym−yt) is stored in the memory 16 as difference scanning position data, and then the processing related to the acquisition of the difference scanning position data is performed. Control for causing the display device 4 to display an image of a character string or the like for notifying the operator of completion is performed on the image generation unit 25d.

  Next, a specific example of a method for acquiring the correction scanning position data stored in the memory 24b will be described.

  For example, a user such as an operator connects each part of the optical scanning observation system 1 before performing observation in the body cavity of the subject, and further performs an operation for turning on the power of the main body device 3. 5 is performed.

  The arithmetic processing unit 25c is a difference stored in advance in the memory 16 when the connector unit 61 of the endoscope 2 and the connector receiving unit 62 of the main unit 3 are connected and the main unit 3 is powered on. Scan position data and reference scan position data stored in advance in the memory 24a are read.

  Then, the arithmetic processing unit 25c outputs each coordinate position data TV (xt, yt) included in the reference scanning position data stored in the memory 24a and each difference data DV included in the difference scanning position data stored in the memory 16. The correction scanning position data is acquired by performing a process of adding (xm−xt, ym−yt), and the acquired correction scanning position data is stored in the memory 24b.

  That is, the correction scanning position data stored in the memory 24b according to the processing of the arithmetic processing unit 25c is obtained when the light irradiation coordinate detection module is actually scanned by the spiral scanning path using the endoscope 2. The same data as each coordinate position data MV (xm, ym) indicating the irradiation position of the illumination light is included.

  By the way, the number of bits required to represent one coordinate position data MV (xm, ym) is, for example, inward of the outermost path including the outermost point B in the spiral scanning path of FIGS. It is considered that it increases in accordance with the expansion of the scanning range of the endoscope 2, which is a region to which it belongs. In a medical system such as the optical scanning observation system 1, for example, a patient circuit formed by an electronic component arranged in a portion that is highly likely to be in direct contact with a subject to be observed and / or treated. And a secondary circuit formed by an electronic component arranged in a portion that is unlikely to be in direct contact with the subject is electrically insulated by an insulating circuit, whereas the insulating circuit is the patient circuit This is a factor that hinders improvement in communication speed between the secondary circuit and the secondary circuit. Therefore, for example, when each coordinate position data MV (xm, ym) obtained by the light irradiation coordinate detection module is directly stored in the memory 16, as the scanning range of the endoscope 2 is expanded, As a result, it takes a long time to complete the reading of the data used for generating the image, and as a result, it takes a long time for the observation image to be displayed on the display device 4 after the main unit 3 is turned on. Problem may occur.

  On the other hand, according to the present embodiment, the difference data DV (xm-xt, ym-yt) that can represent one data with a smaller number of bits than the coordinate position data MV (xm, ym) is stored in the memory. 16 is stored in advance, for example, even when the scanning range of the endoscope 2 is expanded, it is difficult to increase the time until the reading of data used for image generation is completed. The time required from when the power of the main unit 3 is turned on until the observation image is displayed on the display device 4 can be shortened as much as possible.

  Note that the present embodiment is not limited to the case where the subject is scanned by the spiral scanning path, and is also applied to the case where the subject is scanned by another scanning path such as a Lissajous form.

  The present invention is not limited to the above-described embodiments, and it is needless to say that various modifications and applications can be made without departing from the spirit of the invention.

DESCRIPTION OF SYMBOLS 1 Optical scanning observation system 2 Endoscope 3 Main body apparatus 4 Display apparatus 5 Input apparatus 11 Insertion part 15 Actuator part 16 Memory 21 Light source unit 22 Driver unit 23 Detection unit 24a Memory 24b Memory 25 Controller 25a Light source control part 25b Scan control part 25c arithmetic processing unit 25d image generation unit

Japanese Unexamined Patent Publication No. 2012-143265

Claims (5)

An endoscope configured to scan a subject with illumination light emitted from a light source unit and receive return light;
A reference scanning position which is provided in a main body apparatus to which the endoscope can be connected and is information indicating an irradiation position of the illumination light which is a reference when the illumination light is irradiated and the subject is scanned along a predetermined scanning path A first storage unit for storing information;
The illumination light irradiation position when the illumination light is irradiated using the endoscope and the subject is actually scanned by the predetermined scanning path, and the reference scanning position information is provided in the endoscope. A second storage unit that stores differential scanning position information that is information indicating a difference value between the irradiation position of the illumination light included in
A correction provided as a processing result of a process provided in the main device and based on the reference scanning position information read from the first storage unit and the differential scanning position information read from the second storage unit A third storage unit in which the scanning position information is stored;
Using the correction scanning position information read from the third storage unit, an image corresponding to the return light received by the endoscope connected to the main body device is generated and output to the display device. An image generator configured as described above,
An optical scanning observation system comprising:   The optical scanning observation system according to claim 1, wherein the reference scanning position information is information indicating an ideal irradiation position of the illumination light in the predetermined scanning path.   The reference scanning position information indicates an average value of the irradiation position of the illumination light obtained when a plurality of endoscopes connectable to the main body apparatus are used and the subject is actually scanned along the predetermined scanning path. The optical scanning observation system according to claim 1, wherein the optical scanning observation system is information.   The reference scanning position information indicates a median value of the irradiation position of the illumination light obtained when a plurality of endoscopes connectable to the main body apparatus are used and the subject is actually scanned along the predetermined scanning path. The optical scanning observation system according to claim 1, wherein the optical scanning observation system is information.   The illumination light irradiation position included in the reference scanning position information read from the first storage unit and the difference value included in the differential scanning position information read from the second storage unit are added. 2. The apparatus according to claim 1, further comprising an arithmetic processing unit configured to acquire the scanning position information for correction and store the scanning position information for correction in the third storage unit. Optical scanning observation system.

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