JP4127598B2 - Endoscope light source system and endoscope apparatus - 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 an observation site that vibrates with a certain periodicity.
[0002]
[Prior art]
In recent years, endoscope apparatuses for photographing various parts have been put into practical use. For example, there is an endoscope apparatus for observing a site that continuously vibrates at a high speed like a vocal cord when a predetermined sound is continuously uttered. The endoscope apparatus is required to be able to constantly illuminate the periphery of the observation site to observe the state of the entire observation site, or to extract and observe only a specific shape of the observation site during vibration as a still image. The
[0003]
Therefore, conventionally, an endoscope having a strobe light source that emits light intermittently has been used instead of a normal light source that emits light constantly. Such an endoscope enables the above-described various types of photography by performing light emission control in which the light emission timing of the strobe light source is synchronized with the frequency of the vocal cord vibration.
[0004]
However, the above strobe light source is not only expensive, but also has a harmful effect of generating noise, electromagnetic waves, etc. due to flash emission. The noise generated during use is very harsh to the endoscope operator (eg a doctor) and the subject (eg patient). 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 shoots one shape of a portion that vibrates with a constant periodicity as a bright still image without generating adverse effects such as electromagnetic waves that may hinder operation. An object of the present invention is to provide a light source system for an endoscope apparatus.
[0006]
[Means for Solving the Problems]
For this reason, the light source system for an endoscope apparatus according to claim 1 includes a single light source that irradiates continuous light, a light beam converging unit that converges continuous light emitted from the light source, and a light beam that is converged by the light beam converging unit. At least one first aperture large enough to transmit all the luminous flux at the arranged position and synchronized with the frequency of the observation site that vibrates at a predetermined frequency. A dimming means having a first dimming member that is rotationally driven by an axis extending in a direction parallel to the straight traveling direction, and the continuous light emitted from the light source is flashed when the first opening crosses the luminous flux. Is emitted.
[0007]
According to the above configuration, since the flash light is generated from the continuous light using the light control means, it is possible to perform strobe light emission using a normal light source such as a xenon light source without using a strobe light source. Therefore, there is no risk of noise, electromagnetic waves, or the like accompanying strobe light emission, eliminating the discomfort of the photographer and suppressing the influence on other medical devices.
[0008]
Further, by converging the light beam incident on the light control means by the light beam converging means, it is possible to suppress the loss of light quantity when generating the flash light and to illuminate the observation site with brighter flash light.
[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 the detection means, the first light control member 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 further includes phase changing means for changing the phase of the flash emission timing. According to the present invention, since the phase of the light emission timing can be shifted with respect to the vibration of the observation site, it becomes possible to illuminate different shapes of the site during the vibration.
[0011]
According to the fourth aspect of the present invention, it is desirable that the first light control member is rotationally driven so that the phase of the flash emission timing corresponds to the predetermined phase of the waveform detected by the detection means. .
[0012]
In the invention according to claim 5, the phase changing means causes the phase of the light emission timing of the flash generated when the first opening crosses the light beam to shift by a predetermined amount with respect to the waveform detected by the detecting means. It is characterized in that the phase is changed. Thereby, various shapes of the observation site during vibration can be photographed as a still image.
[0013]
According to the light source system for an endoscope apparatus according to claim 6, the phase changing means includes the second opening smaller than the first opening, and is located behind the first dimming member on the optical path, A second dimming member disposed so that the second opening is always in the light beam, and the second dimming member is driven so that the position of the second opening in the light beam is changed; It is desirable to change the phase by
[0014]
The light source system for an endoscope apparatus according to claim 7 further includes a drive unit that drives at least the first light control member so as to be completely retracted from the optical path.
[0015]
According to the present invention, since the continuous light continuously illuminates the observation site by retracting at least the first light control member out of the optical path using the driving means, it is possible to perform normal imaging. Here, not only the first light control member but also the second light control member can be interlocked and retracted out of the optical path.
[0016]
The light source system for an endoscope apparatus according to the present invention is very effective when observing a vocal cord when a predetermined sound is continuously uttered (claim 8). Further, a condensing lens can be used as the light beam converging means.
[0017]
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 (electronic scope) 100b, and a microphone 100c. The processor 100a includes a light source unit 10, a control unit 20, a video processing circuit 30, and a light guide 40. The light source system includes a light source unit 10 and a control unit 20.
[0018]
When the endoscope apparatus 100 is used, a vocal cord that is an observation site is imaged (observed) as follows. First, the microphone 100c is fixed in advance near the patient's throat, and one sound is continuously uttered. The microphone 100c detects the vibration waveform of the vocal cord and transmits it to the control unit 20 as a detection signal. The control unit 20 shapes the detected waveform into a pulse waveform having a certain periodicity. Then, the control unit 20 performs light emission control of the light source unit 10 described in detail below in synchronization with a signal whose waveform has been shaped.
[0019]
Based on the control of the control unit 20, the light emitted from the light source unit 10 illuminates the inside of the body through the light guide 40 from the distal end of the scope 100 b, that is, the light guide distal end 40 a. While the inside of the body is illuminated, the CCD 60 provided at the tip accumulates charges corresponding to the optical image formed on the light receiving surface by the incident light and outputs it to the video signal processing circuit 30. The video signal processing circuit 30 performs predetermined processing based on the input electric charge, and then outputs a video signal to a monitor (not shown). The monitor displays an image corresponding to the video signal.
[0020]
Note that the endoscope operator can operate the operation panel 50 provided in the processor 100a to instruct the control unit 20 regarding photographing. For example, various settings such as switching between various modes such as normal shooting and strobe shooting can be performed.
[0021]
In this specification, an imaging mode (or an observation mode) used when photographing the situation around the observation region and introducing or leading out the distal end of the scope 100b of the endoscope apparatus 100 to the observation region position safely and reliably. Is called normal photography (or normal observation). In addition, a mode in which only one shape of an observation site (continuous vocal cord in this embodiment) in continuous vibration is extracted and photographed and photographed (observed) as a still image is called strobe photographing (or strobe observation).
[0022]
Hereinafter, the light emission control of the light source unit 10 will be described in detail. As shown in FIG. 1, the light source unit 10 includes a xenon light source 1, a first condenser lens 2, a rotary shutter 3, a disc 4, a second condenser lens 5, and a diaphragm 6.
[0023]
FIG. 2 is an enlarged view of the rotary shutter 3 and the disc 4 as viewed from the first condenser lens 2 side obliquely. As shown in FIG. 2, the rotary shutter 3 includes an opening 31, and the disk 4 includes a slit 41. The rotary shutter 3 and the disc 4 are arranged on a plane substantially perpendicular to the optical axis of the first condenser lens 2. In particular, the rotary shutter 3 is disposed at a predetermined position on the optical path where the luminous flux is converged. The opening 31 has a size that allows all the incident light flux to the rotary shutter 3 to pass therethrough. If the rotary shutter 3 is arranged at a position where the light beam is more converged, the opening 31 can be made smaller. If the opening 31 can be made small, the rotary shutter 3 itself can be downsized. If the rotary shutter 3 is reduced in size, there is an advantage that unbalance in the center of gravity balance during rotation can be reduced and stable rotation without shaking can be obtained.
[0024]
FIG. 3 is an enlarged view of the vicinity of the rotary shutter 3 and the disc 4. As shown in FIG. 3, a motor 3 a is connected to the rotary shutter 3, and a motor 4 a is connected to the disc 4. Both the motor 3 a and the motor 4 a are connected to the control unit 20. That is, the control unit 20 controls the rotation of the rotary shutter 3 in a predetermined direction (in the direction of arrow P1 in FIG. 2) via the motor 3a, and drives the disc 4 in the direction of the arrow P2 in FIG. 2 via the motor 4a. Control.
[0025]
The rotary shutter 3 and the disc 4 are held on the base 3c. The base 3c is placed on a pair of rails 3d extending in a direction orthogonal to the straight light traveling direction (in FIG. 3, a direction perpendicular to the paper surface). The base 3c is driven and controlled by the control unit 20 via a rack and gear mechanism (not shown) and a motor 3b, and moves along a pair of rails 3d. By the movement of the base 3c, the rotary shutter 3 and the disc 4 can be inserted into or retracted from the light beam.
[0026]
By configuring the light source unit 10 as described above, in the light source system of the present embodiment, the following light emission control is performed corresponding to the set shooting mode. First, flash control for flash photography will be described. Note that, regardless of which shooting mode is set, the control unit 20 always controls the xenon light source 1 to be on (lighted) while the light source lamp lighting switch on the operation panel 50 is turned on. The xenon light source 1 emits continuous light.
[0027]
At the time of flash photography, the control unit 20 drives the base 3c via the motor 3b and inserts the rotary shutter 3 and the disc 4 into the optical path. Specifically, the rotary shutter 3 and the disc 4 are inserted and arranged in a state in which the opening 31 transmits the entire light beam and the slit 41 is positioned in the light beam.
[0028]
The continuous light emitted from the xenon light source 1 is incident on the rotary shutter 3 while being converged by the first condenser lens 2.
[0029]
The control unit 20 drives the motor 3a at a rotational speed corresponding to the period of the vocal cord vibration waveform detected by the microphone 100c, and rotates the rotary shutter 3. That is, by driving the motor 3a to make one rotation in one cycle of the vocal cord vibration and rotating the rotary shutter 3, continuous light from the xenon light source 1 causes the rotary shutter 3 to be rotated for a predetermined time when the opening 31 crosses the light beam. To Penetrate. As a result, a flash that is emitted only for a predetermined time and necessary for flash photography is generated. Further, the control unit 20 measures the phase relationship between the vibration waveform of the vocal cords and the opening 31 that traverses the light beam by a rotary encoder (not shown) provided near the rotation axis of the rotary shutter 3. Then, the control unit 20 makes the flash emission timing, specifically, the phase of the timing at which the flash passes through the slit 41 and illuminates the observation site, always correspond to the predetermined phase of the vibration waveform corresponding to the desired shape of the vocal cords. The rotary shutter 3 is controlled to rotate. Therefore, the shape of the part illuminated by the flash (that is, imaged) is always the same.
[0030]
As described above, the opening 31 is configured to be large enough to transmit the entire converged light beam. Therefore, for example, compared with the case where continuous light is directly incident on the rotary shutter 3 without passing through the first condenser lens 2, there is almost no light loss when the opening 31 crosses the light beam, and the light beam before passing through the opening 31 (continuous). The amount of light) and the amount of light flux (flash) after passing through the aperture 31 are substantially the same. That is, a brighter flash is generated. Furthermore, since the rotary shutter 3 itself can also be reduced in size, it is possible to generate a flash that emits light for a short time at a smaller number of rotations.
[0031]
The flash generated through the rotary shutter 3 enters the disc 4. The disc 4 makes it possible to finely adjust the phase of the light emission timing of the flash generated by the rotary shutter 3 and change the phase of the vocal cord during flash emission, that is, photograph the subtle shape of the vocal cord during high-speed vibration as a still image. Is provided to do. When a different shape is desired to be captured by changing the phase of the vocal cord during flash emission, the endoscope operator performs a predetermined adjustment operation related to the phase change of the flash emission timing on the operation panel 50.
[0032]
When a predetermined adjustment operation related to the phase change of the flash emission timing is performed from the operation panel 50, the control unit 20 controls driving of the disk 4 via the motor 4a in response to an instruction from the operation panel 50 based on the adjustment operation. (FIG. 3). The control unit 20 moves the disk 4 so that the position of the slit 41 changes in the cross section (dotted line in FIG. 2) of the flash (light beam) incident on the disk 4 after passing through the opening 31. Drive in the direction of the middle arrow P2. By changing the position of the slit 41, the phase of the flash emission timing can be slightly shifted with respect to the vocal cord vibration.
[0033]
For example, as shown in FIG. 2, when the initial setting is performed, when the slit 41 is positioned at a substantially central portion of the light beam cross section, the endoscope operator can change the vocal cord shape at a phase earlier than the phase that can be photographed at present. When the setting is changed so as to shoot, the control unit 20 drives the disk 4 to rotate to the left in FIG. The rotary shutter 3 in FIG. 2 rotates in the direction of the arrow P1. For this reason, the phase of the flash emission timing can be changed earlier with respect to the vibration waveform of the vocal cords by shifting the relative position of the slit 41 with respect to the transmitted light beam cross section of the opening 31 from the substantially central portion to the left side. Similarly, the phase of the flash emission timing can be changed later with respect to the vibration waveform of the vocal cords by rotating the disk to the right in the figure by a predetermined amount and shifting the position of the slit from approximately the center to the right. it can.
[0034]
The flash that has passed through the slit 41 of the disk 4 is guided through the light guide 40 and illuminates the vocal cords from the tip 40a. The above is the light emission control at the time of flash photography.
[0035]
In the above description, it has been described that the control unit 20 drives the disk 4 by a predetermined amount in a predetermined direction each time the setting is changed by the operation panel 50. However, when a specific operation is performed on the operation panel 50, the disk 4 can be automatically driven by a predetermined amount for each period of the vibration waveform of the vocal cords. When the disc 4 is driven in this way, the relative position of the slit 41 with respect to the transmitted light beam cross section of the opening 31 gradually changes, so that it vibrates at high speed like a vocal cord when one sound is continuously uttered. It is also possible to take an image of the observation site to be vibrated (shape change) at a slow speed that is easy for an endoscope operator to observe.
[0036]
Next, light emission control during normal shooting will be described. During normal photographing, the control unit 20 drives the base 3c via the motor 3b to retract the rotary shutter 3 and the disk 4 from the optical path. Continuous light emitted from the xenon light source 1 enters the diaphragm 6 via the first condenser lens 2 and the second condenser lens 5. The diaphragm 6 is controlled by the control unit 20 in accordance with the amount of illumination light set by the operation panel 50 or the like. The continuous light focused to a predetermined light quantity by the diaphragm 6 enters the light guide 40. Then, the observation site is illuminated from the light guide tip 40a provided at the tip of the scope 100b. The above is the light emission control for normal photographing.
[0037]
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.
[0038]
In the present embodiment described above, the xenon light source 1 is used, but other light sources may be used as long as they can emit continuous light. Further, in the present embodiment described above, the first condenser lens 2 is used as means for converging the continuous light irradiated from the xenon light source 1 with respect to the opening 31 of the rotary shutter 3. However, the 1st condensing lens 2 is an example of a light beam converging means to the last, and is not limited to this.
[0039]
For example, an LED array in which a plurality of LEDs are arranged can be used as a light source, and continuous light emitted from the LED array can be converged by a concave mirror.
[0040]
In the above embodiment, the rotary shutter 3 provided with one opening 31 is used. However, it is also possible to use a rotary shutter 3 that is provided with a plurality of openings 31 at a predetermined interval and that is driven and controlled so that one rotation period becomes a value obtained by multiplying the vibration period of the observation site by the number of openings 31. If there are a plurality of openings 31, flashes corresponding to the number of openings 31 can be generated each time the rotary shutter 3 rotates once. However, if too many openings 31 are provided in the rotary shutter 3, the next opening enters the light beam before one opening completely crosses the light beam, which may hinder flash emission. Therefore, it is desirable to use the rotary shutter 3 provided with the optimum number of openings 31 in consideration of the burden on the motor 3a, the required flash emission interval, the emission time, and the like. In the case where a plurality of openings 31 are provided, the openings 31 are arranged symmetrically with respect to the center of the rotary shutter, thereby facilitating balance during rotation and easy control.
[0041]
In the above embodiment, during normal shooting, the rotary shutter 3 and the disc 4 are retracted out of the optical path of continuous light using the motor 3b or the like, but normal shooting can be performed without using this method. . For example, while the rotation of the rotary shutter 3 is stopped in a state where the opening 31 is disposed at a position where the entire continuous light can be transmitted, the observation site can always be illuminated with continuous light even if only the disk 4 is retracted. it can.
[0042]
In the above-described embodiment, the rotation-driven disc 4 provided with the slit 41 is used as a means for shifting the phase of the light emission timing. However, the slit 4 can move the position of the slit in the light beam. If possible, it is possible to use a configuration other than the above configuration. For example, the phase of the light emission timing can be shifted by linearly sliding a rectangular plate having slits instead of the disc 4.
[0043]
In the above embodiment, the disc 4 provided with the slit 41 is provided together with the rotary shutter 3 so that a different shape can be photographed by changing the phase of the vocal cords during flash emission. Is not an essential component for carrying out the present invention. For example, when shooting only a specific state (shape) of the observation site at all times during strobe shooting, such as when shooting only the open state of the vocal cords as a still image, there is no need to provide the disc 4 and rotary What is necessary is just to change the opening 31 of the shutter 3 into the slit 41. Accordingly, the light source unit 10 can also be reduced in size, and the cost of the entire endoscope apparatus 100 can be reduced.
[0044]
In the above-described embodiment, the observation site has been described on the assumption that one sound is a vocal cord during continuous utterance, but the endoscope apparatus 100 is not used only when photographing the vocal cord. For example, it can be used when photographing other vibrating parts such as a heart that continues to beat, and a part that is always in a stationary state can also be photographed. When photographing a vibrating part other than the vocal cords, in some cases, other vibration detection means other than the microphone 100c can be used.
[0045]
Moreover, although the scope 100b in the said embodiment assumes the electronic scope type, even if it is a fiberscope type, it can be used. The scope 100b and the CCD 70 provided in the electronic scope 100b may be of either monochrome or color type.
[0046]
【The invention's effect】
As described above, the present invention can provide an inexpensive and simple light source system by using a single normal light source not only for normal photographing but also for strobe photographing. In addition, since no strobe light source is used, it is possible to avoid all harmful effects on photographing such as electromagnetic waves generated when the strobe light source is used.
[0047]
Furthermore, a brighter flash can be generated by blocking or transmitting the light beam converged by the light beam converging means by the light adjusting means.
Further, since the light control means only needs to have an opening having a size that allows the converged light beam to pass therethrough, the light control means can be reduced in size. As a result, the light control means can be configured to be able to generate a flash that emits light for a short time with a small number of rotations, and a bright still image without blurring can be taken.
[Brief description of the drawings]
FIG. 1 is a schematic configuration diagram of an endoscope apparatus equipped with a light source system according to an embodiment of the present invention.
FIG. 2 is a view of a rotary shutter and a disk of the light source system as viewed from the xenon light source side.
FIG. 3 is an enlarged view of the vicinity of a rotary shutter and a disk of the light source system.
[Explanation of symbols]
DESCRIPTION OF SYMBOLS 1 Xenon light source 2 Condensing lens 3 Rotary shutter 3a Aperture 4 Disc 4a Slit 10 Light source part 20 Control part 100 Endoscope apparatus

Claims (10)

One light source that emits continuous light;
A light beam converging means for causing converging the continuous light emitted from the light source,
A rotary shutter disposed at a convergence position of the light beam, provided with a rotation shaft extending in a direction parallel to the optical axis of the light beam, and rotated in synchronization with the frequency of the observation site that vibrates at a predetermined frequency;
Have
The rotary shutter has at least one first opening provided so as to cross the optical path of the light beam according to the rotation of the rotary shutter,
A continuous light emitted from the light source is emitted as a flash light by the first opening crossing the luminous flux ,
Further comprising phase changing means for changing the phase of the flash emission timing;
A light source system for an endoscope apparatus characterized by the above. 2. The size of the first opening is set so that all of the light beam can pass through the first opening when the first opening is at a convergence position of the light beam. A light source system for an endoscope apparatus according to 1. The light source system for an endoscope apparatus according to claim 1 , further comprising detection means for detecting vibration of the observation site as a waveform. The rotary shutter endoscope apparatus according to claim 3, characterized in that the phase of the light emission timing of the flash to a predetermined phase of the waveform detected by said detecting means is rotated so as to correspond Light source system. To be shifted by a predetermined amount for a given phase of the waveform where the phase of the light emission timing of the flash light is detected by said detection means, according to claim 3 or the phase changing means and changes the phase 5. A light source system for an endoscope apparatus according to 4 . The phase changing means has a disc ;
A second opening smaller than the first opening is formed in the disc ,
The disc is disposed behind the rotary shutter on the optical path so that the second opening is always in the luminous flux,
Said phase changing means, according to any one of claims 1-5, characterized in that for changing the phase by driving the disc as positioned in said light beam of said second opening changes light source system for an endoscope apparatus. The light source system for an endoscope apparatus according to claim 1 , further comprising driving means for driving the rotary shutter so that the rotary shutter is completely retracted from the optical path. The light source system for an endoscope apparatus according to any one of claims 1 to 7, wherein the recording portion is a vocal cord when a predetermined sound is continuously uttered. The light source system for an endoscope apparatus according to any one of claims 1 to 8, wherein the light beam converging means is a condensing lens. In an endoscopic device that normally observes a part that vibrates with periodicity, stroboscopic still photography, or stroboscopic video photography,
A light source system for an endoscope apparatus according to any one of claims 1 to 9,
A scope including an imaging unit that captures an optical image of a tip portion that irradiates light from the light source system and the portion to be illuminated;
An endoscope apparatus characterized by comprising:

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