JP2002365559A - Light source system for endoscope and processor for the endoscope - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a light source system for an endoscope which generates no adverse effect such as electromagnetic wave which has may present risk of hindering the operation and images a single shape of a part, which vibrates with constant periodicity, as a bright stationary picture without blurring. SOLUTION: This light source system for endoscope is composed of a light source which irradiates with continuous light, a first light guide means which guides the continuous light from a first optical path through which the continuous light advances straight, immediately after irradiation of the continuous light from the light source to a second optical path which is parallel with the first optical path but does not lie on the extended line of the first optical path, a second light guide means which guides a light flux which advances straight through the second optical path to a third optical path which is positioned on the extension line of the first optical path and is directed to a light guide and a light control means which is arranged between the first light guiding means and the second light guiding means, has at least one slit and is rotatingly driven with the first period, corresponding to the prescribed period about the axis of extended line of the first optical path.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a light source system mounted on an endoscope apparatus used for observing a portion that vibrates with a constant periodicity.

[0002]

2. Description of the Related Art In recent years, endoscope apparatuses for imaging various parts have been put to practical use. For example, there is an endoscope apparatus for imaging a portion that continuously vibrates at a high speed such as a vocal cord. In an endoscope apparatus for imaging and observing the vibrating part, an imaging method of constantly illuminating the observation part to image the periphery of the observation part and observing it as a moving image on a monitor (hereinafter referred to as normal imaging)
In addition, it is required that an imaging method for capturing a slow moving image (hereinafter, referred to as “slow imaging”) can be performed so that an observation site in high-speed vibration can be observed for a change due to the vibration.

For this reason, an endoscope apparatus provided with a strobe light source that emits light intermittently has been used instead of a normal light source that always emits light. Such an endoscope apparatus enables slow imaging by performing light emission control that synchronizes the light emission timing of a strobe light source with the frequency of vocal cord vibration.

However, the above-mentioned strobe light source is not only expensive, but also has a disadvantage that noise, electromagnetic waves and the like are generated due to light emission. The noise emitted during use is very harsh for the surgeon and the subject. Further generation of electromagnetic waves may cause a malfunction of other medical devices. In other words, there is a problem that is not appropriate for the medical device placed in the examination / treatment room and needs to be solved immediately.

[0005]

SUMMARY OF THE INVENTION Accordingly, in view of the above circumstances, the present invention has been made in consideration of the above circumstances, and does not cause any adverse effects such as electromagnetic waves or the like, which may interfere with operation of the device. It is an object of the present invention to provide a light source system for an endoscope apparatus capable of performing not only normal imaging but also slow imaging, and a processor equipped with the light source system.

[0006]

According to the present invention, there is provided a light source system for an endoscope apparatus for imaging an observation site which vibrates at a predetermined cycle. is there. And a light source for irradiating continuous light;
The incident continuous light is guided from the first optical path where the continuous light travels straight after being irradiated from the light source to the second optical path which is parallel to the first optical path and is not on an extension of the first optical path. A first light guide means, a second light guide means for directing a light beam traveling straight on the second light path to a third light path toward the light guide, which is located on an extension of the first light path, and It is arranged between the light guide means and the second light guide means, has at least one slit, and is rotationally driven around an extension of the first optical path at a first cycle corresponding to the predetermined cycle. Light control means. Here, the first light guiding means and the second light guiding means rotate at a second cycle based on a predetermined cycle about an extension of the first optical path, and the slit goes straight through the second optical path. The continuous light emitted from the light source is emitted as strobe light by traversing the continuous light.

[0007] According to the above arrangement, the stroboscopic light is generated from the continuous light by rotating the two light guiding means and the dimming means having the slit, respectively. Strobe light emission can be performed using any ordinary light source. Therefore, there is no possibility that noise, electromagnetic waves or the like are generated due to the strobe light emission, the operator's discomfort is eliminated, and the influence on other medical devices can be suppressed.

[0008] Further, by providing dimming means, which is rotationally controlled at the same cycle as the vibration cycle of the observation site, between the two light guide means rotating at a predetermined cycle, the vibration cycle of the observation site can be reduced. To change the flash firing cycle.
Accordingly, it is possible to perform slow imaging without clear blur.

A light source system for an endoscope apparatus according to a second aspect of the present invention is characterized in that the light source system further comprises a detecting means for detecting the vibration of the observation site as a waveform. By using the waveform detected by the detection means, the rotation of the light control means can be performed accurately in synchronization with the frequency of the vibrating part.

[0010] A light source system for an endoscope apparatus according to a third aspect of the present invention is characterized in that it has a rotation cycle changing means for arbitrarily changing the second cycle. According to the present invention, the rotation speed of the first light guide and the second light guide can be arbitrarily changed, so that slow imaging of the operator at any speed can be performed.

According to the invention described in claim 4, the second cycle can be made substantially the same as the first cycle. This also enables normal imaging.

According to the fifth aspect of the present invention, the light control means has a disk shape, and the slit of the light control means is
It is desirable to extend in the radial direction.

According to a sixth aspect of the present invention, in the light source system for an endoscope apparatus, the first light guide and the second light guide have the same structure. Thereby, parts can be shared and the manufacturing cost can be reduced.

According to the light source system for an endoscope apparatus according to the present invention, each light guide means is a disk provided with a through-hole extending radially from a central portion. It is preferable that at least two deflecting members are fitted, and that each light guide unit guides the incident light beam to a predetermined optical path by deflecting the incident light beam at least twice by the deflecting member.

According to the eighth aspect of the present invention, each of the light guiding means and the dimming means is disposed in a plane orthogonal to an extension of the first optical path, and each of the deflecting members is provided with an incident light. It is desirable to deflect the luminous flux by about 90 degrees. With this configuration, the entire light source system can be downsized. Design and manufacturing are also easier.

[0016] If the first light guide means and the second light guide means are rotationally driven by a common motor, a light source system having a simpler configuration can be provided.

According to a further aspect of the present invention, there is provided a processor for an endoscope apparatus, comprising: a light source system as described above; Data storing means for storing, and output means for reading out the image data stored first in the data storing means at a predetermined timing and outputting the read out data to a monitor, wherein the image data for a predetermined frame is stored. The storage unit is characterized in that no new data writing process is performed. With this configuration, a slow moving image can be observed without any trouble even when the vibration period of the observation site is much shorter than the monitor period.

[0018]

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 device 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 100b has a light guide 150 and a CCD 160. The light source system
The light source unit 110 and the control unit 120 are included.

FIG. 2 is a schematic configuration diagram of the light source unit 110. As shown in FIG. 2, the light source unit 110 includes the normal light source 1, and the first light guide member 2,
A rotary shutter 3 and a second light guide member 4 are provided. The light source unit 110 includes a first motor 5, a second motor 6
Having. The normal light source 1 is a light source that emits continuous light, and includes, for example, a xenon lamp. Although not shown in FIG. 2, the light source unit 110 is also provided with a stop 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 beam, and the like. I have.

Each of the first light guide member 2, the rotary shutter 3, and the second light guide member 4 has a disk shape. Each of the members 2, 3, and 4 has an optical path (hereinafter, referred to as a first optical path) of a continuous light emitted from a normal light source at substantially the center of each plane portion.
It is arranged so as to be orthogonal to the extension of L1.

Inside the first light guide member 2, there is provided a through-hole 21 extending from the central portion in the radial direction by a predetermined length. FIG. 3 is a diagram illustrating a cross-sectional shape of the first light guide member 2 on a plane including the first optical path L1 and the through hole 21. The opening 21a on the one surface A side of 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, substantially coincides with the center of the surface A. It is formed. The length of the opening 21a in the radial direction is set to be substantially the same as or larger than the diameter of the cross section of the light beam entering the opening 21a by traveling straight through the first optical path. The opening 21b on the other surface B side of the through hole 21 has the same shape as the opening 21a and is formed on the most circumferential side of the through hole 21.
Right angle prisms 22 and 23 are fitted as deflecting means in the vicinity of the openings 21a and 21b so that a light beam incident from one opening is emitted from the other opening. Each of the right-angle prisms 22 and 23 has a respective opening 21a,
The surfaces 22a and 23a on the 21b side are fitted so as to be parallel to the surfaces A and B, respectively. Each right-angle prism 22, 2
3 so that the through holes 21 can be fitted in a more stable state.
Are formed such that the cross-sectional shape becomes a parallelogram (see FIG. 3).

The first light guide member 2 having the above structure is arranged such that the surface A is usually on the light source 1 side. Thus, continuous light emitted from the normal light source 1 always enters the opening 21a.

In the present embodiment, the first light guide member 2 and the second light guide member 4 have the same structure. Accordingly, in FIG. 2, the numbers corresponding to the configurations of the above-described first light guide member are assigned to the second light guide member 4, and the detailed description is omitted. As described above, the common use of the parts achieves a reduction in the manufacturing cost and an increase in the efficiency of the manufacturing operation.

However, the second light guide member 4 has a circumferential opening 4.
1 b is disposed so as to face the opening 21 b on the circumferential side of the first light guide member 2 with the rotary shutter 3 interposed therebetween. That is, the second light guide member 4 is disposed such that the surface B is on the rotary shutter 3 side. Each of the light guide members 2 and 4 is disposed such that the rotation angles of the openings 21b and 41b on the surface B side with respect to the extension of the first optical path L1 are the same. Thus, the light beam emitted from the opening 21 b of the first light guide member 2 always enters the opening 41 b via the rotary shutter 3.

The first light guide member 2 and the second light guide member 4 are
The common first motor 5 and the drive unit 7 including a pulley, a belt and the like are driven to rotate at a constant speed to each other. 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 rotating shaft 7c, and the respective pulleys 7d and 7e also rotate in response to the rotation of the rotating shaft 7c. Each pulley 7d,
The rotation of 7e is transmitted to each light guide member 2, 4 via the second belt 7f and the third belt 7g.

The rotary shutter 3 has a slit 31. The second motor 6 rotationally drives the rotary shutter 3 via the fourth belt 8a. As will be described later, both the first motor 5 and the second motor 6
The drive is controlled by 0.

The first light guide member 2, the rotary shutter 3, and the second light guide member 4 have side surfaces (each belt 7f, 7f, 7g, 8a) so that the respective belts 7f, 7g, 8a can rotate stably without vibration. 7g and 8a are rotatably held by a plurality of rollers (not shown). A sensor (not shown) for detecting a rotation state is provided near each of the members 2, 3, and 4.

By configuring the light source unit 110 as described above, the following light emission control is performed according to the set imaging mode. At the time of imaging, the surgeon fixes the microphone 100c near the throat of the subject, and has the subject utter a predetermined sound continuously in cooperation with the subject.

The control unit 120 always controls lighting of the normal light source 1 as long as the light source lamp lighting switch on the front panel switch 140 is turned on, regardless of which imaging mode is set. Also, during imaging, the microphone 100c
, A vocal cord vibration waveform is detected. After the vibration waveform is pulse-shaped, it is transmitted to the control unit 120 as a detection signal.

The control unit 120 calculates the vibration period of the vocal cords using the detection signal, and controls the driving of 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 located at a predetermined rotation angle with respect to the extension of the first optical path L1, the vocal cord as the observation site always has a shape corresponding to the predetermined phase of the vibration waveform.

First, the light emission control when the slow imaging is set will be described in detail. At the time of slow imaging, the operator operates the front panel switch 140 to make settings relating to slow imaging. Specifically, it sets how many wavelengths of vocal cord vibration are divided for imaging. The greater the number of divisions that is set, the smaller the degree of change in the shape of the vocal cords that is imaged per image (light emission). That is, the time required to capture one wavelength of the vocal cord vibration becomes longer, and the operator can observe a moving image reproduced at a lower speed.

The control section 120 controls the driving of the first light guide member 2 and the second light guide member 4 based on the set division number. The control unit 120 first divides the rotation cycle of the rotary shutter 3 (that is, the vibration cycle of the vocal cords) by the set number of divisions, and obtains the rotation cycle of each of the light guide members 2 and 4. Then, the first motor 5 is driven and controlled based on the calculation result, and the light guide members 2 and 4 are rotated.

Normally, continuous light emitted from the 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 rectangular prism 22). The continuous light incident on the through-hole 21 is converted into a right-angle prism 22
After being deflected by approximately 90 degrees on the inclined surface 22b, the right-angle prism 2
2 exits from the surface 22 c of the right-angle prism 23
c. 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 is in the same plane as the first optical path L1 and in the second optical path L2 parallel to the first optical path L1.
Go straight on.

Here, since the first light guide member 2 is rotating, the second light path L2 (and the luminous flux that travels straight through the second light path L2) just travels around the extension of the first light path L1. It is in a state where it revolves at the same speed as the rotation speed of the member 2 (or the second light guide member 4). The rotary shutter 3 rotates at a much higher speed than the light guide members 2 and 4. Therefore, continuous light traveling straight through the second optical path L2 passes through the rotary shutter 3 only when the slit 31 crosses the second optical path L2. The operation of transmitting or blocking continuous light is repeated by the rotary shutter 3 to generate pseudo strobe light from the continuous light.

More specifically, the strobe light is generated once per rotation of the rotary shutter 3, and the set number of strobe lights per rotation of each of the light guide members 2, 4 (one round of the second optical path L2). Light is generated. 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 number of divisions. In other words, the strobe light is emitted once per cycle of the vocal cord vibration waveform, and the phase of the generation (emission) of the strobe light is shifted by the predetermined amount from the phase of the vibration waveform.

For example, if the set number of divisions is 30, one vocal fold vibration for one wavelength is observed in 30 frames. That is, the rotary shutter 3 makes 30 rotations while each of the light guide members 2, 4 makes one rotation. The predetermined amount is π / 15. That is, the change in the shape of the vocal cords between two consecutive frames is π / 15.

The strobe light travels straight through the second optical path L2, and the aperture 41b of the second light guide member 4 (the surface 43 of the right angle prism 43).
a). Then, the strobe light is transmitted to the second light guide member 4.
Of the right angle prism 43 in the through hole 41 of FIG.
b, surface 43c, surface 42c of right angle prism 42, inclined surface 42
b, the surface 42a (the opening 41a of the second light guide member 4)
Emitted from. That is, in the through hole 41, the strobe light is guided on an optical path opposite to that in the through hole 21 of the first light guide member 2.

The strobe light emitted from the second light guide member 4 travels straight through the third optical path L3 on the extension of the first optical path L1, and enters the light guide 150 disposed on the extension of the first optical path L1. Incident. The above is the description of the light emission control at the time of slow imaging. The imaging processing and the image processing using the strobe light generated as described above will be described below.

The strobe light is guided inside the light guide 150 and emits light from the tip of the scope section 100b. When in the light emitting state, the CCD 160 provided at the tip is
The electric charge corresponding to the optical image formed on the light receiving surface by the light reflected and incident on the observation site is accumulated. The control unit 120
First light guide member 2, rotary shutter 3, second light guide member 4
The generation (emission) timing of the strobe light is detected based on the rotation state of the first light guide member 2, the rotary shutter 3, and the second light guide member 4 transmitted from the above-mentioned sensor (not shown) provided near the camera. And the CCD1
A charge read pulse is transmitted to 60. CCD160
Outputs the stored charge as an image signal to the video processing circuit 130 in response to the charge readout pulse.

The image signal is converted into A /
After performing predetermined digital processing such as D conversion, the image data is sequentially written into the frame memory 131 (FIG. 1) as image data corresponding to one frame. And the video processing circuit 13
“0” is sequentially read out from the image data written first in the frame memory 131 in synchronization with a vertical synchronization signal transmitted at a predetermined timing from the control unit 120, and performs predetermined processing such as D / A conversion to perform video processing. Monitor 100
Output to d. 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 from the phase of the vibration waveform, the image displayed on the monitor is the same as the moving image reproduced at the speed corresponding to the setting of the operator. Has become. In addition, light used for imaging is strobe light generated by the first light guide member 2, the rotary shutter 3, and the second light guide member 4 in a pseudo manner, so that an image without blur can be obtained.

Note that the number of image data that can be written to the frame memory 131 is limited. In addition, the oscillation 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
Suspends the writing process so that the image data is already written and is not overwritten, and the monitor 100
On d, a smooth slow moving image is always ensured.

The above is the imaging processing and image processing of the endoscope apparatus 100 when the slow imaging is set. By performing the slow imaging, the observation site that vibrates at a high speed, such as a vocal cord when one sound is continuously uttered, is vibrating (shape changing) at a speed desired by the operator. It is possible to image and observe. Next, light emission control and the like when the operator sets normal imaging will be outlined.

At the time of normal imaging, the control unit 120
In a state where 1 is in the second optical path L2, the first light guide member 2 and the second light guide member 4 are rotated by the rotation cycle of the rotary shutter 3,
In other words, the rotation is controlled at the same cycle as the vibration cycle of the vocal cords. The control unit 120 determines whether the slit 31 is in the second optical path L2 using a sensor. Thus, the continuous light emitted 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 that is deflected by the second light guide member and illuminates the observation site via the light guide 150 is a light beam that is continuously emitted.

The control unit 120 transmits a charge read pulse to the CCD 160 at the same timing as the transmission timing of the vertical synchronizing signal, unlike during slow imaging.
The CCD 160 always stores charges except during the period of reading charges.

The video processing circuit 130 performs a predetermined process on the image signal transmitted from the CCD 160, and temporarily writes the image data in the frame memory 131 (FIG. 1). Then, 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 addition, unlike the slow imaging described above, imaging is performed based on the transmission cycle of the vertical synchronization signal during normal imaging.
31 will never be full. That is, the video processing circuit 13
A value of 0 does not interrupt the data writing process during normal imaging. The above is the description at the time of normal imaging.

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 gist.

In the above-described embodiment, the light guide member is formed by providing a through hole in the disk and fitting the prism into the through hole, but the light guide member is not limited to this structure. 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.

In the above embodiment, in order to further reduce the size of the light source unit 110 and to reduce the work load at the time of manufacturing, the first light guide member 2 is perpendicular to the extension of the first optical path L1.
The rotary shutter 3 and the second light guide member 4 are provided, and each prism is configured to deflect an incident light beam at a substantially right angle. However, the arrangement configuration of each of the members 2, 3, and 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. It is possible.

The setting of the slow imaging performed by the surgeon at the time of the slow imaging does not necessarily set how many wavelengths of the vibration of the observation region are divided as in the above-described embodiment. The amount of change in the shape of the observation region between the two (the amount of change in the phase of the vibration cycle) may be input. When the amount of change is set, a slower moving image reproduced at a lower speed can be observed as the set amount of change is smaller.

In the above embodiment, when the frame memory 131 is full during slow imaging, the video processing circuit 130 interrupts data writing to the frame memory 131, thereby preventing overwriting. However, other methods are also possible. For example, when an image signal of a predetermined level or less is transmitted, the video processing circuit 130 is set to ignore the signal. Then, when the frame memory 131 is full, the control unit 120 may turn off (turn off) the normal light source.

In the above-described embodiment, the control unit 1 operates at the time of normal imaging.
20 guides continuous light to the light guide 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. If it is in the two light path L2,
The rotation of each member 2, 3, 4 may be stopped.

In the above-described embodiment, the observation site has been described assuming that one sound is a vocal cord during continuous vocalization. However, the endoscope apparatus 100 is not used only when imaging a vocal cord. For example, it can also be used when imaging other vibrating parts, such as a beating heart. When imaging a vibrating part other than the vocal cords, in some cases, other vibration detecting means other than the microphone 100c can be used.

Further, the scope 10 in the above embodiment is used.
Although 0b is assumed to be an electronic scope type, a fiber scope type in which a TV camera is installed (removably) on an eyepiece can also be used. Further, the CCD 160 provided in the electronic scope 100b may be either monochrome or color type.

[0054]

As described above, according to the present invention, since a strobe light is simulated by using a single normal light source, not only normal imaging but also slow imaging can be performed. It is possible to provide a light source system that hardly affects equipment.

[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 device 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 the light source unit.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Normal light source 2 First light guide member 3 Rotary shutter 4 Second light guide member 22, 23, 42, 43 Right angle prism 110 Light source unit 120 Main control unit 130 Video processing circuit 131 Frame memory 100 Endoscope device 100a Processor

 ──────────────────────────────────────────────────続 き Continuing on the front page (72) Inventor Hiroyuki Kobayashi 2-36-9 Maenocho, Itabashi-ku, Tokyo Asahi Gaku Kogyo Co., Ltd. (72) Inventor Minoru Matsushita 2-36-9 Maenocho, Itabashi-ku, Tokyo No. Asahi Gaku Kogyo Co., Ltd. F-term (reference) 2H040 BA09 BA23 CA04 CA06 CA09 CA10 GA02 GA11 4C061 GG01 RR03 RR18

Claims (12)

[Claims] 1. A light source system used for an endoscope apparatus for imaging an observation site that vibrates at a predetermined cycle, wherein the light source irradiates continuous light, and the incident continuous light is radiated from the light source. First light guiding means for guiding a continuous light straight from the first optical path to a second optical path parallel to the first optical path and not on an extension of the first optical path, A second light guiding unit that guides a light beam that travels straight through the second optical path to a third optical path that is located on an extension of the first optical path and that is directed to a light guide, the first light guiding unit and the second light guiding unit. A light control means that is disposed between the light guide means and has at least one slit, and is rotationally driven around an extension of the first optical path at a first cycle corresponding to the predetermined cycle; Wherein the first light guide means and the second light guide means extend the first light path. Rotating at a second cycle based on the predetermined cycle around a line, continuous light emitted from the light source is emitted as strobe light by the slit traversing continuous light traveling straight through the second optical path. Light source system for an endoscope device. 2. The light source system for an endoscope apparatus according to claim 1, further comprising a detection unit for detecting a vibration cycle of the observation site. 3. The endoscope according to claim 1, wherein the light source system for an endoscope apparatus further comprises a rotation cycle changing unit for arbitrarily changing the second cycle. Light source system for equipment. 4. The light source system for an endoscope device according to claim 3, wherein the second cycle is substantially the same as the first cycle. . 5. The light source system for an endoscope device according to claim 1, wherein the light control means has a disk shape, and the slit extends in a radial direction. A light source system for an endoscope device, which is provided. 6. The light source system for an endoscope according to claim 1, wherein the first light guide and the second light guide have the same structure. , A light source system for an endoscope device. 7. The light source system for an endoscope apparatus according to claim 6, wherein each of the light guides is a disk having a through hole extending from a central portion in a radial direction. A light source for an endoscope device, wherein at least two deflecting members are fitted, and each light guide means guides the incident light beam to a predetermined optical path by deflecting the incident light beam at least twice by the deflecting member. system. 8. The light source system for an endoscope apparatus according to claim 7, wherein each of the light guide means and the dimming means are disposed in a plane orthogonal to an extension of the first optical path, respectively. A light source system for an endoscope apparatus, wherein each deflecting member deflects an incident light beam by approximately 90 degrees. 9. The light source system for an endoscope device according to claim 7, wherein each deflection member is a right-angle prism. 10. The light source system for an endoscope according to claim 1, wherein the first light guide and the second light guide are rotationally driven by a common motor. Light source system for an endoscope device. 11. A light source system for an endoscope apparatus according to claim 1, wherein image data relating to an observation region imaged using strobe light emitted from the light source unit is provided in a predetermined frame. Data storage means for storing the image data, and output means for sequentially reading out the image data stored in the data storage means at a predetermined timing and outputting the read image data to a monitor. The processor for an endoscope apparatus according to claim 1, wherein new data writing processing is not performed on the stored data storage means. 12. The processor for an endoscope apparatus according to claim 11, wherein the observation region is a vocal cord when a predetermined sound is uttered continuously.