JP4716469B2 - Endoscope light source system and endoscope device processor - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to a light source system mounted on an endoscope apparatus used for observing a site that vibrates with a certain periodicity.
[0002]
[Prior art]
In recent years, endoscope apparatuses that image various parts have been put into practical use. For example, there is an endoscope apparatus for imaging a part that continuously vibrates at high speed such as a vocal cord. In the endoscope apparatus for imaging and observing the vibration part, not only an imaging method (hereinafter referred to as normal imaging) in which the observation part is constantly illuminated to image the periphery of the observation part and observed as a moving image on the monitor. In addition, it is required that an imaging method (hereinafter referred to as slow imaging) that captures a moving image as a slow moving image so that an observation site in high-speed vibration can be observed due to the vibration.
[0003]
Therefore, conventionally, an endoscope apparatus including a strobe light source that emits light intermittently has been used instead of a normal light source that emits light constantly. Such an endoscope apparatus enables slow imaging by performing light emission control that synchronizes the light emission timing of the strobe light source with the frequency of vocal cord vibration.
[0004]
However, the strobe light source is not only expensive, but also has a harmful effect that noise, electromagnetic waves, etc. are generated with light emission. The noise generated during use is very harsh to the operator and the subject. Furthermore, if electromagnetic waves are generated, other medical devices may malfunction. In other words, there is a problem that should not be solved immediately, which is not suitable for a medical device placed in an examination / treatment room.
[0005]
[Problems to be solved by the invention]
Therefore, in view of the above circumstances, the present invention provides not only normal imaging but also slow imaging of a shape of a portion that vibrates with a certain periodicity without generating adverse effects such as electromagnetic waves that may hinder operation. It is an object of the present invention to provide a light source system for an endoscope apparatus that can be used and a processor equipped with the light source system.
[0006]
[Means for Solving the Problems]
For this reason, the light source system for an endoscope apparatus according to claim 1 is a light source system used for an endoscope apparatus that images an observation site that vibrates with a predetermined period. Then, a light source that emits continuous light and an incident continuous light from a first optical path in which the continuous light travels straight after being irradiated from the light source are parallel to the first optical path and an extension of the first optical path A first light guide means for guiding a second optical path that is not on the line, and a light beam that travels straight along the second optical path is positioned on the extension line of the first optical path and is guided to the third optical path toward the light guide. The first light guide means, the first light guide means and the second light guide means, having at least one slit and having a first period corresponding to the predetermined period, Dimming means for rotationally driving about an extension line of the optical path as an axis. Here, the first light guide means and the second light guide means rotate in a second period based on a predetermined period with the extension line of the first optical path as an axis, and the slit goes straight through the second optical path. The continuous light emitted from the light source is emitted as strobe light by crossing the continuous light.
[0007]
According to the above configuration, since the strobe light is generated from the continuous light by rotating the two light guide means and the light control means having the slits, a normal xenon light source such as a xenon light source is used without using a strobe light source. Strobe light can be emitted using a light source. Therefore, there is no risk of noise, electromagnetic waves, or the like accompanying strobe light emission, the operator's discomfort is eliminated, and the influence on other medical devices can be suppressed.
[0008]
In addition, a dimming device whose rotation is controlled at the same cycle as the oscillation cycle of the observation site is disposed between two light guides that rotate at a predetermined cycle, so that strobe light emission is performed with respect to the oscillation cycle of the observation site. The period can be changed. Therefore, it is possible to perform slow imaging without sharp blur.
[0009]
The light source system for an endoscope apparatus according to a second aspect of the present invention further includes detection means for detecting vibration of the observation site as a waveform. By using the waveform detected by this detection means, the light control means can be driven to rotate in synchronization with the frequency of the vibration part.
[0010]
The light source system for an endoscope apparatus according to claim 3 includes a rotation period changing unit that arbitrarily changes the second period. According to the present invention, by allowing the rotational speeds of the first light guide unit and the second light guide unit to be arbitrarily changed, the operator can perform slow imaging at an arbitrary speed.
[0011]
According to invention of Claim 4, a 2nd period can be made substantially the same as a 1st period. This also enables normal imaging.
[0012]
According to the invention described in claim 5, it is desirable that the light control means has a disc shape, and the slit of the light control means extends in the radial direction.
[0013]
The light source system for an endoscope apparatus according to claim 6 is characterized in that the first light guide means and the second light guide means have the same structure. As a result, the parts can be shared and the manufacturing cost can be reduced.
[0014]
According to the light source system for an endoscope apparatus according to claim 7, each light guide means is a disc including a through hole extending in the radial direction from the center portion, and at least two of the through holes are provided in the through hole. One deflecting member is fitted, and each light guide means desirably guides the incident light beam to a predetermined optical path by deflecting the incident light beam at least twice by the deflecting member.
[0015]
According to the invention described in claim 8, each light guide means and said light control means are respectively disposed in a plane perpendicular to the extension line of the first optical path, and each deflecting member receives each incident light beam. It is desirable to deflect approximately 90 degrees. With this configuration, the entire light source system can be reduced in size. Design and manufacture are also easy.
[0016]
Further, if the first light guide unit and the second light guide unit are rotationally driven by a common motor, a light source system having a simpler configuration can be provided.
[0017]
Furthermore, the processor for an endoscope apparatus according to claim 11 stores data for a predetermined frame of image data relating to an observation site imaged using the light source system as described above and strobe light emitted from the light source unit. A data storage means having a storage means and an output means for reading out the image data stored first in the data storage means in order at a predetermined timing and outputting the data to a monitor; Is characterized in that no new data writing process is performed. With such a configuration, a slow moving image can be observed without hindrance even when the vibration period of the observation site is much shorter than the monitor period.
[0018]
DETAILED DESCRIPTION OF THE INVENTION
FIG. 1 is a schematic configuration diagram of an endoscope apparatus 100 equipped with a light source system according to an embodiment of the present invention. The endoscope apparatus 100 includes a processor 100a, a scope unit 100b, a microphone 100c, and a monitor 100d. The processor 100a includes a light source unit 110, a control unit 120, a video processing circuit 130, and a front panel switch 140. The scope unit 100 b includes a light guide 150 and a CCD 160. The light source system includes a light source unit 110 and a control unit 120.
[0019]
FIG. 2 is a schematic configuration diagram of the light source unit 110. As shown in FIG. 2, the light source unit 110 has a normal light source 1, and a first light guide member 2, a rotary shutter 3, and a second light guide member 4 are disposed in order from the normal light source 1 side. Yes. The light source unit 110 includes a first motor 5 and a second motor 6. The normal light source 1 is a light source that emits continuous light, such as a xenon lamp. Although not shown in FIG. 2, the light source unit 110 is appropriately provided with a diaphragm for reducing the amount of continuous light emitted from the normal light source 1, a collimating lens for converting the continuous light into a parallel light flux, and the like. Yes.
[0020]
The first light guide member 2, the rotary shutter 3, and the second light guide member 4 all have a disk shape. Each member 2, 3, 4 is disposed so as to be orthogonal to an extension line of a continuous light path (hereinafter referred to as a first optical path) L <b> 1 irradiated from a normal light source at the approximate center of each plane portion. .
[0021]
Inside the first light guide member 2, a through hole 21 extending from the central portion in a radial direction by a predetermined length is provided. FIG. 3 is a diagram illustrating a cross-sectional shape of the first light guide member 2 on a surface including the first optical path L <b> 1 and the through hole 21. The opening 21a on the one surface A side in the through hole 21 has a rectangular shape extending in the radial direction, and its center is on the first optical path L1, that is, coincides with the approximate center of the surface A. It is formed. The length of the opening 21a in the radial direction is configured to be substantially the same as or larger than the diameter of the cross section of the light beam that travels straight along the first optical path and enters the opening 21a. The opening 21 b on the other surface B side in the through hole 21 has the same shape as the opening 21 a and is formed on the most circumferential side of the through hole 21. In the vicinity of the openings 21a and 21b, right-angle prisms 22 and 23 are fitted as deflection means so that a light beam incident from one opening is emitted from the other opening. The right-angle prisms 22 and 23 are fitted so that the surfaces 22a and 23a on the side of the openings 21a and 21b are parallel to the surfaces A and B, respectively. Further, the through hole 21 is formed so that the cross-sectional shape is a parallelogram so that the right-angle prisms 22 and 23 can be fitted in a more stable state (see FIG. 3).
[0022]
The 1st light guide member 2 of the said structure is arrange | positioned so that the surface A may exist in the normal light source 1 side. Thereby, the continuous light irradiated from the normal light source 1 always enters the opening 21a.
[0023]
In the present embodiment, the first light guide member 2 and the second light guide member 4 have the same structure. Therefore, regarding the second light guide member 4, in FIG. 2, the number corresponding to the configuration of the first light guide member described above is attached, and the detailed description is omitted. In this way, by sharing parts, it is possible to reduce the manufacturing cost and increase the efficiency of the manufacturing work.
[0024]
However, the second light guide member 4 is disposed such that the circumferential opening 41b faces the circumferential opening 21b of the first light guiding member 2 with the rotary shutter 3 interposed therebetween. That is, the second light guide member 4 is disposed so that the surface B is on the rotary shutter 3 side. The light guide members 2 and 4 are arranged such that the rotation angles with respect to the extension line of the first optical path L1 of the openings 21b and 41b on the surface B side are the same. Thereby, the light beam emitted from the opening 21 b of the first light guide member 2 is always incident on the opening 41 b via the rotary shutter 3.
[0025]
The first light guide member 2 and the second light guide member 4 are rotationally driven at a constant speed by a common first motor 5 and a drive unit 7 including a pulley, a belt, and the like. Specifically, the rotation of the first motor 5 is first transmitted by the first belt 7a to the first pulley 7b and the rotating shaft 7c that holds the first pulley 7b. A second pulley 7d and a third pulley 7e are held on the rotary shaft 7c, and the pulleys 7d and 7e also rotate in accordance with the rotation of the rotary shaft 7c. The rotations of the pulleys 7d and 7e are transmitted to the light guide members 2 and 4 through the second belt 7f and the third belt 7g.
[0026]
The rotary shutter 3 includes a slit 31. The second motor 6 rotationally drives the rotary shutter 3 via the fourth belt 8a. As will be described later, the first motor 5 and the second motor 6 are both driven and controlled by the control unit 120.
[0027]
Further, the first light guide member 2, the rotary shutter 3, and the second light guide member 4 are provided on the side surfaces (each belt 7f, 7g, 8a) so that the belt 7f, 7g, 8a can be stably rotated without shaking. Are held rotatably by a plurality of rollers (not shown). A sensor (not shown) for detecting the rotation state is provided in the vicinity of each member 2, 3, 4.
[0028]
By configuring the light source unit 110 as described above, the following light emission control is performed corresponding to the set imaging mode. During imaging, the surgeon fixes the microphone 100c near the subject's throat and continuously utters a predetermined sound in cooperation with the subject.
[0029]
Regardless of which imaging mode is set, the control unit 120 always controls the lighting of the normal light source 1 while the light source lamp lighting switch on the front panel switch 140 is on. At the time of imaging, a vibration waveform of a vocal cord is detected from the microphone 100c. The vibration waveform is pulse-shaped and then transmitted to the control unit 120 as a detection signal.
[0030]
The control unit 120 calculates the vibration period of the vocal cords using the detection signal, and drives and controls the second motor 6 so that the rotary shutter 3 rotates at the same period as the vibration period. Therefore, when the slit 31 is positioned at a predetermined rotation angle with respect to the extended line of the first optical path L1, the vocal cords as the observation site always have a shape corresponding to the predetermined phase of the vibration waveform.
[0031]
First, the light emission control when the slow imaging is set will be described in detail. At the time of slow imaging, the surgeon operates the front panel switch 140 to make settings related to slow imaging. Specifically, it is set how many wavelengths of one vibration of the vocal cord are divided to be imaged. If the number of divisions to be set is set to be large, the degree of change in the shape of the vocal cords captured for each imaging (light emission) is reduced accordingly. That is, the time required to image one wavelength of the vocal cord vibration becomes longer, and the surgeon can observe a moving image reproduced at a slower speed.
[0032]
The control unit 120 performs drive control of the first light guide member 2 and the second light guide member 4 based on the set number of divisions. The controller 120 first divides the rotation period of the rotary shutter 3 (that is, the vocal cord vibration period) by the set number of divisions to obtain the rotation period of each light guide member 2, 4. Based on the calculation result, the first motor 5 is driven and controlled to rotate the light guide members 2 and 4.
[0033]
The continuous light emitted from the normal light source 1 travels straight through the first optical path L1 and enters the through hole 21 through the opening 21a of the first light guide member (the surface 22a of the right-angle prism 22). The continuous light that has entered the through-hole 21 is deflected by approximately 90 degrees on the inclined surface 22 b of the right-angle prism 22, is then emitted from the surface 22 c of the right-angle prism 22, and is incident on the surface 23 c of the right-angle prism 23. The continuous light incident on the surface 23c is deflected by approximately 90 degrees on the inclined surface 23b of the right-angle prism 23, and then emitted from the surface 23a of the right-angle prism 23 (the opening 21b of the first light guide member). The emitted continuous light travels straight in a second optical path L2 that is in the same plane as the first optical path L1 and parallel to the first optical path L1.
[0034]
Here, since the first light guide member 2 is rotating, the second light path L2 (and the light beam traveling straight along the second light path L2) is exactly the first light guide member 2 ( Or it is in the state which is revolving at the same speed as the rotational speed of the 2nd light guide member 4). The rotary shutter 3 rotates at a speed much faster than the light guide members 2 and 4. Therefore, the continuous light traveling straight in the second optical path L2 is transmitted through the rotary shutter 3 only when the slit 31 crosses the second optical path L2. By repeating the operation of transmitting or blocking the continuous light by the rotary shutter 3, strobe light is artificially generated from the continuous light.
[0035]
Specifically, strobe light is generated once for each rotation of the rotary shutter 3, and strobe light is generated for the number of divisions set for each rotation of the light guide members 2 and 4 (one turn of the second optical path L2). Is done. Further, the positions (rotation angles) of the slit 31 and the second optical path L2 when two continuous strobe lights are generated are shifted by a predetermined amount obtained by dividing 2π by the division number. That is, the strobe light is emitted once every period of the vocal cord vibration waveform, and the phase of the generation (light emission) timing of the strobe light is shifted by the predetermined amount with respect to the phase of the vibration waveform.
[0036]
For example, when the set number of divisions is 30, one vibrational wavelength of the vocal cord is observed in 30 frames. That is, the rotary shutter 3 rotates 30 times while the light guide members 2 and 4 rotate once. The predetermined amount is π / 15. That is, the change in the vocal cord shape between two consecutive frames is π / 15.
[0037]
The strobe light travels straight along the second optical path L2 and enters the opening 41b (the surface 43a of the right-angle prism 43) of the second light guide member 4. The strobe light passes through the inclined surface 43b and the surface 43c of the right-angle prism 43 and the surface 42c and the inclined surface 42b of the right-angle prism 42 in the through-hole 41 of the second light-guide member 4. From the opening 41a). That is, in the through hole 41, the strobe light is guided along the opposite optical path to that in the through hole 21 of the first light guide member 2.
[0038]
The strobe light emitted from the second light guide member 4 travels straight through the third optical path L3 on the extension line of the first optical path L1 and enters the light guide 150 disposed on the extension line of the first optical path L1. The above is the description of the light emission control at the time of slow imaging. An imaging process and an image process using the strobe light generated as described above will be described below.
[0039]
The strobe light is guided through the light guide 150 and emitted from the tip of the scope unit 100b. When in the light emitting state, the CCD 160 provided at the tip accumulates charges corresponding to the optical image formed on the light receiving surface by the light reflected and incident at the observation site. The control unit 120 includes a first light guide member 2, a rotary shutter 3, a first light guide member 2, a rotary shutter 3, which are transmitted from the above-described sensor (not shown) provided in the vicinity of the second light guide member 4. The generation (light emission) timing of the strobe light is detected based on the rotation state of the second light guide member 4, and a charge read pulse is transmitted to the CCD 160 simultaneously with the generation of the strobe light. In response to the charge readout pulse, the CCD 160 outputs the accumulated charge as an image signal to the video processing circuit 130.
[0040]
The image signal is subjected to predetermined digital processing such as A / D conversion in the video processing circuit 130 and then sequentially written in the frame memory 131 (FIG. 1) as image data corresponding to one frame. Then, the video processing circuit 130 sequentially reads the image data written in the frame memory 131 first in synchronization with the vertical synchronization signal transmitted from the control unit 120 at a predetermined timing, and performs a predetermined process such as D / A conversion. The image is processed and output to the monitor 100d as a video signal. The monitor 100d displays an image corresponding to the video signal. As described above, since the phase of the light emission timing is shifted by the predetermined amount with respect to the phase of the vibration waveform, the image displayed on the monitor is a moving image reproduced at a speed corresponding to the setting of the operator. It has become. Moreover, since the light used for imaging is the strobe light that is artificially generated by the first light guide member 2, the rotary shutter 3, and the second light guide member 4, a blur-free image is obtained.
[0041]
There is a limit to the number of image data that can be written to the frame memory 131. In addition, the vibration period of the vocal cords is much faster than the transmission period of the vertical synchronization signal. Therefore, the frame memory 131 may become full while the imaging operation is repeated. In this case, the video processing circuit 130 interrupts the writing process so that the image data is already written and is not overwritten, so that a smooth slow moving image is always ensured on the monitor 100d.
[0042]
The above is the imaging processing and image processing of the endoscope apparatus 100 when the slow imaging is set. By performing slow imaging, the observation site that vibrates at high speed like the vocal cords when a single sound is uttered continuously vibrates (changes in shape) at the speed desired by the operator. Imaging and observation are possible. Next, an outline of light emission control and the like when the surgeon sets normal imaging will be described.
[0043]
During normal imaging, the control unit 120 causes the first light guide member 2 and the second light guide member 4 to rotate with the rotation period of the rotary shutter 3, in other words, vocal cord vibration, with the slit 31 in the second optical path L2. The rotation is controlled at the same cycle as the cycle. The control unit 120 determines whether the slit 31 is in the second optical path L2 using a sensor. Thereby, the continuous light irradiated from the normal light source 1 is always transmitted through the slit 31 after being deflected by the first light guide member 2. That is, the light beam deflected by the second light guide member and illuminates the observation site via the light guide 150 is a light beam by continuous light emission.
[0044]
Also, unlike the slow imaging, the control unit 120 transmits a charge readout pulse to the CCD 160 at the same timing as the transmission timing of the vertical synchronization signal. The CCD 160 always accumulates charges except during a period in which charges are read.
[0045]
The video processing circuit 130 performs predetermined processing on the image signal transmitted from the CCD 160 and temporarily writes it as image data in the frame memory 131 (FIG. 1). In synchronization with the vertical synchronization signal, the image data is read from the frame memory 131 and output to the monitor 100d as a video signal. In the normal imaging, unlike the slow imaging, the imaging is performed based on the transmission cycle of the vertical synchronization signal, so that the frame memory 131 does not become full. That is, the video processing circuit 130 does not interrupt the data writing process during normal imaging. The above is the explanation for normal imaging.
[0046]
The above is the embodiment of the present invention. The present invention is not limited to these embodiments, and various modifications can be made without departing from the spirit of the present invention.
[0047]
In the present embodiment described above, the light guide member is configured by providing a through hole in the disk and inserting a prism therein, but the light guide member is not limited to this configuration. For example, a notch extending from the circumference to the center instead of the through hole may be formed, and a prism may be fitted at a predetermined position of the notch. Another deflecting member such as a total reflection mirror may be used instead of the prism.
[0048]
Moreover, in the said embodiment, in order to reduce the light source part 110 further and to reduce the work burden at the time of manufacture, the 1st light guide member 2, the rotary shutter 3, and 2nd so that it may orthogonally cross the extended line of the 1st optical path L1. The light guide member 4 is provided, and each prism is configured to deflect the incident light beam substantially at a right angle. However, the arrangement configuration of the members 2, 3, 4 and the deflection direction of the prism are not limited to the configuration, and can be flexibly deformed in relation to the arrangement positions of other members constituting the processor 100a. Is possible.
[0049]
The settings related to the slow imaging performed by the surgeon during the slow imaging do not necessarily set how many wavelengths of one vibration of the observation site are divided as in the above embodiment, but for example, between two consecutive frames The amount of change in the shape of the observation site (the amount of change in phase of the vibration period) may be input. When setting the amount of change, the smaller the amount of change to be set, the more slowly moving images that are reproduced at a slower speed can be observed.
[0050]
In the above-described embodiment, when the frame memory 131 is full during slow imaging, the video processing circuit 130 interrupts data writing to the frame memory 131 to prevent overwriting. However, other methods are possible. For example, when an image signal having a predetermined level or less is transmitted, the video processing circuit 130 is set to ignore the signal. When the frame memory 131 is full, the control unit 120 may be configured to turn off (turn off) the normal light source.
[0051]
In the above embodiment, during normal imaging, the control unit 120 writes continuous light by rotating the first light guide member 2, the rotary shutter 3, and the second light guide member 4 at the same period as the vibration period of the vocal cords. Although guided to the guide, if the slit 31 is in the second optical path L2, the rotation of the members 2, 3, and 4 may be stopped.
[0052]
In the above-described embodiment, the observation site is described on the assumption that one sound is a vocal cord during continuous utterance, but the endoscope apparatus 100 is not used only when imaging the vocal cord. For example, it can be used when imaging other vibrating parts such as a heart that continues to beat. When imaging a vibrating part other than the vocal cords, depending on the case, vibration detection means other than the microphone 100c can be used.
[0053]
Further, although the scope 100b in the above embodiment is assumed to be an electronic scope type, it can be used even if it is a fiberscope type in which a TV camera is installed (detachable) on an eyepiece. The CCD 160 provided in the electronic scope 100b may be either monochrome or color type.
[0054]
【The invention's effect】
As described above, the present invention has a configuration in which a strobe light is artificially generated using a single normal light source, so that it is possible to perform not only normal imaging but also slow imaging and affects other devices. Therefore, it is possible to provide a light source system with less.
[Brief description of the drawings]
FIG. 1 is a schematic configuration diagram of an endoscope apparatus according to an embodiment of the present invention.
FIG. 2 is a schematic configuration diagram of a light source unit of the endoscope apparatus according to the embodiment of the present invention.
FIG. 3 is an enlarged view of a cross section of a first light guide member of a light source unit.
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 1 Normal light source 2 1st light guide member 3 Rotary shutter 4 2nd light guide member 22,23,42,43 Right angle prism 110 Light source part 120 Main control part 130 Image processing circuit 131 Frame memory 100 Endoscope apparatus 100a Processor

Claims (12)

A light source system used in an endoscope apparatus that images an observation site that vibrates with a predetermined cycle,
A light source that emits continuous light;
Incident continuous light is changed from a first optical path in which the continuous light travels straight after being irradiated from the light source to a second optical path that is parallel to the first optical path and not on an extension line of the first optical path. A first light guiding means for guiding;
A second light guide means for guiding a light beam traveling straight along the second optical path to a third optical path located on an extension line of the first optical path toward the light guide;
The first optical path is extended between the first light guide means and the second light guide means, has at least one slit, and has a first period corresponding to the predetermined period. Dimming means for rotationally driving the wire as an axis,
The first light guide means and the second light guide means rotate in a second period based on the predetermined period with an extension line of the first optical path as an axis,
A light source system for an endoscope apparatus, wherein continuous light emitted from the light source is emitted as strobe light as the slit crosses continuous light traveling straight through the second optical path. The light source system for an endoscope apparatus according to claim 1, further comprising:
A light source system for an endoscope apparatus, characterized by comprising detection means for detecting a vibration period of the observation site. The light source system for an endoscope apparatus according to claim 1 or 2,
A light source system for an endoscope apparatus, comprising: a rotation period changing unit that arbitrarily changes the second period. The light source system for an endoscope apparatus according to claim 3,
The light source system for an endoscope apparatus, wherein the second cycle is substantially the same as the first cycle. The endoscope light source system according to any one of claims 1 to 4,
The light control means has a disc shape,
The light source system for an endoscope apparatus, wherein the slit extends in a radial direction. The light source system for an endoscope apparatus according to any one of claims 1 to 5,
The first light guide means and the second light guide means have the same structure, and the light source system for an endoscope apparatus is characterized in that: The light source system for an endoscope apparatus according to claim 6,
Each light guide means is a disc having a through hole extending in the radial direction from the center portion,
At least two deflecting members are fitted in the through hole,
Each light guide means guides an incident light beam to a predetermined optical path by deflecting an incident light beam at least twice by the deflecting member. The light source system for an endoscope apparatus according to claim 7,
Each light guide unit and the light control unit are respectively disposed in a plane orthogonal to the extension line of the first optical path,
The light source system for an endoscope apparatus, wherein each deflecting member deflects each incident light beam by approximately 90 degrees. The light source system for an endoscope apparatus according to claim 7 or 8,
Each deflection member is a right-angle prism, The light source system for endoscope apparatuses characterized by things. The light source system for an endoscope apparatus according to any one of claims 1 to 9,
The light source system for an endoscope apparatus, wherein the first light guide unit and the second light guide unit are rotationally driven by a common motor. A light source system for an endoscope apparatus according to any one of claims 1 to 10,
Data storage means for storing image data relating to an observation site imaged using strobe light emitted from the light source unit for a predetermined frame;
Output means for reading out the image data stored first in the data storage means in order at a predetermined timing and outputting it to a monitor;
A processor for an endoscope apparatus, wherein a new data writing process is not performed in the data storage means in which the image data for a predetermined frame is stored. The processor for an endoscope apparatus according to claim 11,
The processor for an endoscope apparatus, wherein the observation site is a vocal cord when a predetermined sound is continuously uttered.

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