JP5624930B2 - Endoscope device - Google Patents

Description

  The present invention relates to an endoscope apparatus.

  In general, an endoscope apparatus includes an endoscope having an insertion portion that is inserted into a subject, and a light source device that supplies illumination light to the endoscope. The endoscope and the light source device are separated from each other. It is configured. As a light source of the light source device, a white light lamp such as a xenon lamp or a metal halide lamp is widely used. However, there is one that generates illumination light using a laser light source instead of the lamp. For example, in the endoscope device disclosed in Patent Document 1, light from a semiconductor laser light source mounted on a light source device is transmitted to the distal end of an endoscope using an optical fiber that is a light guide member, and the insertion portion White light is emitted through a phosphor provided at the tip.

  By the way, when illuminating light is transmitted between the light source device and the distal end of the insertion portion of the endoscope using a single optical fiber or a small number of optical fibers, the illumination light is generated even if a part of the optical fiber is broken. The effect of optical transmission loss on the light intensity increases, and the amount of illumination light is greatly reduced. For this reason, there is a technique for detecting optical transmission loss such as disconnection of the optical fiber. For example, Patent Document 2 describes a light-emitting device that utilizes the fact that a phosphor disposed at an emission end of an optical fiber is heated by laser light irradiation. In this light-emitting device, the disconnection is detected by determining whether the light from the light source reaches the phosphor by observing the temperature change of the phosphor.

JP 2008-73346 A JP 2008-122838 A

  However, the light-emitting device of Patent Document 2 indicates whether the light transmission loss occurred in either the light guide member in which the wavelength conversion member is disposed at the light exit end or the light guide member in which the light diffusion member is disposed at the light exit end. It could not be detected using one temperature sensor.

  The present invention uses a single temperature sensor to determine which light transmission loss occurs between a light guide member having a wavelength conversion member disposed at a light exit end and a light guide member having a light diffusion member disposed at a light exit end. It is an object of the present invention to provide an endoscope apparatus that can detect the above.

The present invention has the following configuration.
An endoscope apparatus having a function of detecting optical transmission loss,
A first light source;
A first light guide member that introduces output light of the first light source and guides it to a distal end of an insertion portion that is inserted into a subject;
A wavelength conversion member disposed at a light exit end of the first light guide member;
A second light source;
A second light guide member for introducing the output light of the second light source and guiding the light to the tip of the insertion portion;
A light diffusing member disposed at a light exit end of the second light guide member;
Light source driving means for generating a drive signal corresponding to a target light amount set for each of the first light source and the second light source, and driving the first light source and the second light source;
A temperature sensor for detecting a temperature due to heat generated from the wavelength conversion member and the light diffusion member;
The first temperature change rate due to heat generation of the wavelength conversion member corresponding to the intensity of the drive signal of the first light source, and the second due to heat generation of the light diffusion member corresponding to the intensity of the drive signal of the second light source. Storage means for storing the temperature change rate of
A third temperature change rate of the temperature detected by the temperature sensor is compared with the first temperature change rate and the second temperature change rate, and the third temperature change rate is the first temperature. When the rate of change coincides with the second light guide member, it is determined that a light transmission loss has occurred. When the rate of change of the third temperature coincides with the rate of change of the second temperature, the first light guide member is determined. An optical transmission loss detecting means for determining that an optical transmission loss has occurred in the optical member;
An endoscopic apparatus comprising:

  According to the endoscope apparatus of the present invention, it is determined whether the light transmission loss occurs in either the light guide member in which the wavelength conversion member is disposed at the light exit end or the light guide member in which the light diffusion member is disposed at the light exit end. It can be detected using a single temperature sensor.

FIG. 1 is a diagram for explaining an embodiment of the present invention, and is a configuration diagram of an endoscope apparatus representing an endoscope and each apparatus to which the endoscope is connected. It is an external view which shows the specific structural example of an endoscope apparatus. It is an expansion perspective view of an endoscope front-end | tip part. It is a disassembled perspective view which shows the structure of an illumination optical system unit. It is principal part sectional drawing which shows the structure of fluorescent substance periphery. It is a graph which shows the spectral characteristic of emitted light. It is a flowchart of the procedure which implements optical transmission loss confirmation control mode. It is a graph which shows the mode of the time change of the temperature detection value by a temperature sensor. It is a block diagram which shows the control content of each information. It is explanatory drawing which shows a mode that the temperature detection value from a temperature sensor changes according to the target light quantity of the laser light source which changes sequentially according to an observation object, and the change of target light quantity. It is a front view of the endoscope front-end | tip part which concerns on the modification with which 2 pairs of 1st light sources and 3rd light sources were provided. It is a block diagram of the light source device which concerns on the modification shown in FIG. It is a graph which shows the spectral characteristic of the light absorbency of a reduced hemoglobin and an oxygenated hemoglobin. It is a graph which shows the value of S1 / S3 and the two-dimensional map which represented the magnitude of the value of S2 / S3 by the orthogonal two axes.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
FIG. 1 is a diagram for explaining an embodiment of the present invention. FIG. 1 is a configuration diagram of an endoscope apparatus representing an endoscope and each apparatus to which the endoscope is connected. FIG. 2 is a specific example of the endoscope apparatus. It is an external view which shows a structural example.
As shown in FIG. 1, the endoscope apparatus 100 includes an endoscope 11, a control device 13, a display unit 15 such as a monitor, and an input unit 17 such as a keyboard and a mouse that input information to the control device 13. It has. The control device 13 includes a light source device 19 and a processor 21 that performs signal processing of a captured image.

  The endoscope 11 includes a main body operation unit 23 and an insertion unit 25 that is connected to the main body operation unit 23 and is inserted into a subject (body cavity). A universal cord 27 is connected to the main body operation unit 23. The distal end of the universal cord 27 is connected to the light source device 19 via a light guide connector 29 and connected to the processor 21 via a video connector 31.

  As shown in FIG. 2, the main body operation unit 23 of the endoscope 11 includes an air / water supply button for performing suction, air supply, and water supply on the distal end side of the insertion unit 25, a shutter button at the time of imaging, and the details. Various operation buttons such as an optical transmission loss confirmation button 33 described later are provided. The main body operation unit 23 is provided with a pair of angle knobs 35 together with these buttons.

  The insertion portion 25 is configured by a flexible portion 37, a bending portion 39, and an endoscope distal end portion 41 that is the distal end of the insertion portion 25 in order from the main body operation portion side. The bending portion 39 is remotely bent by rotating the angle knob 35 of the main body operation portion 23, whereby the endoscope distal end portion 41 can be directed in a desired direction.

  FIG. 3 is an enlarged perspective view of the distal end portion 41 of the endoscope. An observation window 43 of the imaging optical system, a first illumination window 45 and a second illumination window 47 of the illumination optical system are arranged at the endoscope distal end portion 41. The first illumination window 45 and the second illumination window 47 are arranged on both sides of the observation window 43. Reflected light from the subject due to illumination light emitted from the first illumination window 45 and the second illumination window 47 is imaged by the imaging element 49 (see FIG. 1) through the observation window 43. The captured observation image is displayed on the display unit 15 connected to the processor 21.

  The imaging optical system includes an imaging element 49 such as a charge coupled device (CCD) type image sensor or a complementary metal oxide semiconductor (CMOS) type image sensor. Further, the imaging optical system includes an optical member 51 (see FIG. 1) such as a lens that forms an observation image on the imaging element 49. The observation image formed and captured on the light receiving surface of the image sensor 49 is converted into an electric signal and input to the image signal processing unit 55 of the processor 21 through the signal cable 53, and converted into a video signal by the image signal processing unit 55. Is done.

  On the other hand, as shown in FIG. 1, the illumination optical system includes a light source device 19, a first optical fiber 59 that is a first light guide member 57 connected to the light source device 19, and a second light guide member 61. A second optical fiber 63. A wavelength conversion member 65 is disposed at the light exit end of the first optical fiber 59, and a light diffusion member 67 is disposed at the light exit end of the second optical fiber 63. The light source device 19 includes a first light source 69 and a second light source 71. The first light source 69 includes a laser light source LD1 that is a semiconductor light emitting element, and a laser light source LD2-A. The second light source 71 includes a laser light source LD2-B that is a semiconductor light emitting element. The light source device 19 includes a light source control unit 75 that is a light source driving unit and a combiner 77. The light source control unit 75 drives and controls the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B. The combiner 77 combines the light emitted from the laser light source LD1 and the laser light source LD2-A and introduces the light into the first optical fiber 59. The light emitted from the laser light source LD2-B is directly introduced into the second optical fiber 63 without being combined.

  The 1st optical fiber 59 and the 2nd optical fiber 63 consist of a single line optical fiber. By using a single optical fiber, the diameter of the insertion portion 25 can be reduced.

  The endoscope distal end portion 41 includes a distal end rigid portion (not shown) therein. The distal end hard portion is made of a metal such as stainless steel, and a plurality of through holes are formed along the longitudinal direction. Various components such as an imaging optical system, an illumination optical system unit 81, a forceps channel 83, and an air / water supply channel communicating with the air / water supply nozzle 85 are attached to each through hole of the distal rigid portion.

  The illumination optical system unit 81 includes a wavelength conversion optical system unit 89 and a light diffusion optical system unit 91 that are arranged symmetrically with respect to the observation window 43. The wavelength conversion optical system unit 89 and the light diffusion optical system unit 91 have substantially the same configuration, and differ depending on whether the wavelength conversion member 65 or the light diffusion member 67 is provided at the light exit end. Here, the wavelength conversion optical system unit 89 provided with the wavelength conversion member 65 will be illustrated and described.

  FIG. 4 is an exploded perspective view showing the configuration of the illumination optical system unit 81. The wavelength conversion optical system unit 89 includes a single mode first optical fiber 59, a wavelength conversion member 65, a ferrule 95 as a holding member that holds the wavelength conversion member 65 and the first optical fiber 59, and the wavelength conversion member 65. A cylindrical sleeve member 97 that covers the outer periphery and a protective cover 99 that seals the tip of the sleeve member 97 are configured. The outer peripheral surface of the first optical fiber 59 is covered with a protection tube (not shown).

  On the other hand, the light diffusing optical system unit 91 includes a second optical fiber 63, a light diffusing member 67, a ferrule 95, a sleeve member 97, and a protective cover 99, as in FIG. In the light diffusing optical system unit 91, the ferrule 95 holds the light diffusing member 67 and the second optical fiber 63 in the same manner as the wavelength conversion optical system unit 89. The sleeve member 97 covers the outer periphery of the ferrule 95, and the protective cover 99 is configured to seal the tip of the sleeve member 97.

  The ferrule 95 is formed in a cylindrical shape and has an insertion hole 103 through which the first optical fiber 59 is inserted. A phosphor holder 105 that holds the wavelength conversion member 65 is formed on the tip side of the ferrule 95. The phosphor holding portion 105 is formed in a concave shape that is concave from the ferrule tip surface 107 according to the outer shape of the wavelength conversion member 65, and the tip side facing the protective cover 99 is opened. The insertion hole 103 is continuous with the proximal end of the phosphor holder 105.

  A reflection film 109 is provided on the surface of the phosphor holder 105. The reflective film 109 is made of a metal film such as silver or aluminum, and is formed into a thin film by, for example, plating, vapor deposition, sputtering, or the like. The wavelength conversion member 65 is held inside the phosphor holding unit 105 while being in contact with the reflective film 109. The illumination light emitted from the wavelength conversion member 65 is reflected by the reflection film 109 and can be used efficiently. When the wavelength conversion member 65 is held by the phosphor holding unit 105, the tip surfaces of the wavelength conversion member 65 and the reflective film 109 are formed so as to be flush with the tip surface of the ferrule 95. The insertion hole 103 is formed along the central axis of the ferrule 95. The first optical fiber 59 is held at the rear end of the wavelength conversion member 65 by fitting the distal end portion thereof into the insertion hole 103.

  FIG. 5 is a cross-sectional view of the main part showing the configuration around the phosphor. The sleeve member 97 is formed in a cylindrical shape having a receiving portion 111 that receives the protective cover 99 and a fitting hole 113 into which the outer peripheral surface of the ferrule 95 is fitted in order from the tip side. The receiving part 111 has a larger inner diameter than the fitting hole 113. The receiving portion 111 has a receiving portion inner peripheral surface 115 that faces the outer peripheral surface of the protective cover 99, and a receiving portion bottom surface 119 that intersects the receiving portion inner peripheral surface 115 and faces the protective cover base end surface 117. The protective cover 99 is adhered to the receiving portion 111 with an adhesive 123 including glass beads 121, whereby the tip of the sleeve member 97 is sealed. The fitting hole 113 is continuous from the bottom surface to the rear end surface of the sleeve member 97 along the center of the sleeve member 97.

  The protective cover 99 can transmit the illumination light emitted from the wavelength conversion member 65, that is, the blue laser light transmitted while diffusing the phosphor, and the green to yellow fluorescence excited and emitted from the wavelength conversion member 65. It is formed into a disk shape from the material. The protective cover 99 is made of, for example, quartz glass or sapphire glass.

  On the other hand, the light diffusion member 67 of the light diffusion optical system unit 91 transmits the illumination light emitted from the laser light source LD2-B while diffusing it. The light diffusing member 67 is formed of, for example, quartz glass or sapphire glass similar to the protective cover 99.

  A laser light source LD1 shown in FIG. 1 is a blue-emitting semiconductor laser having a central wavelength of 445 nm. As this laser light source LD1, for example, a broad area type InGaN laser diode can be used. The laser light source LD2-A and the laser light source LD2-B are violet-emitting semiconductor lasers having a central wavelength of 405 nm. As this laser light source LD1, for example, a broad area type InGaN laser diode can be used.

  The light source controller 75 controls the output light intensity, lighting timing, and the like of the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B. The output light of these laser light sources is introduced into the first optical fiber 59 and the second optical fiber 63 via the light guide connector 29. The introduced output light is transmitted to the endoscope distal end portion 41 through the insertion portion 25 by the first optical fiber 59 and the second optical fiber 63, and is irradiated to the wavelength conversion member 65 and the light diffusion member 67. The wavelength conversion member 65 emits the output light from the laser light source LD1 and the laser light source LD2-A and the emitted light wavelength-converted by the wavelength conversion member 65 to the first illumination window 45. The light diffusing member 67 transmits the output light from the laser light source LD <b> 2 -B to the second illumination window 47 almost through the light. From the first illumination window 45 and the second illumination window 47, the light source controller 75 can control the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B to emit light of any intensity at any timing. It has become.

FIG. 6 is a graph showing the spectral characteristics of the emitted light. The wavelength conversion member 65 absorbs a part of the blue laser light emitted from the laser light source LD1 and emits a plurality of kinds of phosphors (for example, YAG-based phosphors or BAM (BaMgAl ₁₀ O ₁₇ )) that emits green and yellow light. Etc.). As shown in FIG. 6, the wavelength conversion member 65 combines the blue laser light from the laser light source LD1 with the green to yellow excitation light obtained by wavelength-converting the blue laser light. , White light indicated by the profile Pf2 is generated.

  The violet laser light emitted from the laser light source LD2-A has a small amount of wavelength-converted light from the wavelength conversion member 65, and most of the violet laser light is emitted as narrow-band light having a center wavelength of 405 nm as shown by a profile Pf1 in FIG. The That is, the laser light source LD2-A outputs narrowband wavelength light having a spectrum different from that of white light. Similarly, LED2-B is emitted as narrowband light having a center wavelength of 405 nm.

  Thereby, the wavelength light which has a specific function can be selectively irradiated, and desired endoscopic observation can be performed with the appropriate wavelength light according to the observation purpose. The center wavelength of the narrow-band wavelength light is 380 nm to 480 nm, preferably 400 nm to 450 nm. Thereby, the fine structure of the capillary blood vessel on the tissue surface layer and the fine structure pattern of the mucosal tissue surface layer can be emphasized and observed.

  Laser light output from each laser light source LD1, laser light source LD2-A, and laser light source LD2-B is guided to the endoscope distal end portion 41 by the first optical fiber 59 or the second optical fiber 63. The guided laser beam selectively emits white light and purple narrow-band light at an arbitrary mixing ratio from the first illumination window 45 or the first illumination window 45 and the second illumination window 47. Can do. The endoscope control unit 127 outputs a desired control signal to the light source control unit 75 for the intensity of the emitted light and the color of the emitted light.

  Based on this control signal, the light source controller 75 outputs a drive signal for driving the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B. The laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B are adjusted by emitting light with an amount of light based on the input drive signal. That is, the light source control unit 75 generates a drive signal corresponding to the set target light amount, and drives the first light source 69 and the second light source 71, respectively.

  By using a phosphor for the wavelength conversion member 65, light having an arbitrary wavelength can be easily generated. Further, since the output light from the first light source 69 and the fluorescence from the wavelength conversion member 65 are combined to form white light, white light is generated using the fluorescence of the phosphor having a broad wavelength spectrum. The Thereby, the color rendering property of illumination light can be improved.

  Here, the white light referred to in the present specification is not limited to one that strictly includes all wavelength components of visible light. For example, it is sufficient if it includes light of a specific wavelength band such as R (red), G (green), B (blue) which are reference colors, and light including wavelength components from green to red or from blue. Light including a wavelength component over green is also broadly included.

  In the vicinity of the wavelength conversion member 65 of the endoscope distal end portion 41, one temperature sensor 129 for detecting the temperature due to heat generated from the wavelength conversion member 65 and the light diffusion member 67 is provided. The temperature sensor 129 is a single sensor disposed between the wavelength conversion member 65 and the light diffusion member 67 at the distal end of the insertion portion 25. The temperature sensor 129 can detect an optical transmission loss with a simple configuration by being a single sensor. Compared to the configuration in which the temperature sensor 129 is provided in each of the wavelength conversion member 65 and the light diffusion member 67, it is advantageous to reduce the diameter of the endoscope 11.

  The temperature sensor 129 detects the temperature due to the heat of the wavelength conversion member 65 generated at the time of wavelength conversion by laser light irradiation and the heat of the light diffusion member 67 generated by the absorption when the laser light is transmitted. The temperature sensor 129 outputs the detected temperature as a temperature detection value to the endoscope control unit 127 through the temperature detection signal line 131.

  As the temperature sensor 129, a thermistor, a thermocouple, or a resistance temperature detector can be used. The temperature sensor 129 is preferably provided at a position as close as possible to both the wavelength conversion member 65 and the light diffusion member 67, and is provided at a position where the wavelength conversion member 65 and the light diffusion member 67 have the same heat conduction coefficient. desirable.

  As shown in FIG. 1, the processor 21 includes an endoscope control unit 127, an imaging signal processing unit 55 that generates a video signal, and a storage unit 135 that is a storage unit such as a RAM that stores the imaging signal and various types of information. And an image processing unit 137. The endoscope control unit 127 performs appropriate image processing on the image data of the observation image output from the imaging signal processing unit 55 by the image processing unit 137 and causes the display unit 15 to display the image data. In addition, a control signal is output to the light source controller 75 of the light source device 19 so that a desired amount of illumination light is emitted from the first illumination window 45 and the second illumination window 47. The endoscope control unit 127 is connected to a network such as a LAN (not shown) and controls the entire endoscope apparatus 100 such as distributing information including image data.

  In the endoscope apparatus 100 having the above-described configuration, the optical transmission loss caused by the endoscope control unit 127 in the normal control mode for performing endoscope observation, the disconnection of the first optical fiber 59 and the second optical fiber 63, and the like. It is possible to switch to an optical transmission loss confirmation control mode for confirming.

  In the normal control mode, desired illumination light is irradiated with a predetermined amount of light by white illumination by the laser light source LD1, simultaneous lighting of the laser light sources LD1 and LD2-A, simultaneous lighting or individual lighting by the laser light sources LD1 and LD2-B. Control to acquire and display an observation image.

  On the other hand, in the optical transmission loss confirmation control mode, control for detecting optical transmission loss between the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B to the first illumination window 45 and the second illumination window 47. I do. The detection of the light transmission loss includes the light guide connector 29, the light path in the light source device, and the light transmission loss of the combiner 77. That is, the detection of the disconnection described below includes the possibility of each of the above optical transmission losses.

Hereinafter, the optical transmission loss confirmation control mode will be described.
FIG. 7 is a flowchart of a procedure for implementing the optical transmission loss confirmation control mode.
The timing for executing the optical transmission loss confirmation control mode is the timing when the power switch of the control device 13 is turned on, and the operator presses the optical transmission loss confirmation button 33 provided on the main body operation unit 23 of the endoscope 11. The timing, the timing when an instruction from the input unit 17 is given, and the like can be arbitrarily set.

  When the optical transmission loss confirmation control mode starts, the endoscope control unit 127 (see FIG. 1) performs exposure control that optimizes the amount of illumination light based on the luminance information of the imaging signal output from the imaging element 49. . By this exposure control, the endoscope control unit 127 sets target light amounts of the laser light source LD1, laser light source LD2-A, and laser light source LD2-B (St1), and a control signal for setting the target light amount to the light source control unit 75. Output. The light source controller 75 controls the output light intensity of the laser light source LD1, laser light source LD2-A, and laser light source LD2-B to the target light amount based on the input control signal (St2).

  Output light from the laser light source LD1 and the laser light source LD2-A driven with the target light quantity is introduced into the first optical fiber 59 and irradiated to the wavelength conversion member 65. Further, the output light from the laser light source LD2-B is introduced into the second optical fiber 63 and irradiated onto the light diffusion member 67. Then, the wavelength conversion member 65 converts the wavelength of the irradiated blue laser light and generates heat. Also, heat is generated when a part of the violet laser beam is wavelength-converted. The light diffusing member 67 transmits the irradiated purple laser light and absorbs a part thereof to generate heat. This heat generation is propagated by the endoscope distal end portion 41 to raise the temperature of each member accommodated in the endoscope distal end portion 41. This temperature change is detected by the temperature sensor 129 (St3).

FIG. 8 shows how the temperature detection value by the temperature sensor 129 changes over time.
The wavelength conversion member 65 and the light diffusing member 67 can be regarded as two heating elements because their temperatures rise due to light irradiation through the first optical fiber 59 and the second optical fiber 63. The inclination of the temperature rise is larger in the wavelength conversion member 65. The temperature rising tendency of these two heating elements is detected by one temperature sensor 129 in the vicinity. The light generated in either the first optical fiber 59 or the second optical fiber 63 by comparing the slope of the temperature rise detected by the temperature sensor 129 with the first temperature change rate and the second temperature change rate. Transmission loss can be detected.

  More specifically, the wavelength conversion member 65 emits fluorescence at a wavelength of 500 to 600 nm by excitation light having a wavelength of 445 nm. This is defined as a first heat generation characteristic Sq1 based on the first temperature change rate. The light diffusing member 67 is for forming a predetermined irradiation angle in order to irradiate the living body with excitation light having a wavelength of 405 nm as special observation light. This is defined as a second heat generation characteristic Sq2 by the second temperature change rate. The first heat generation characteristic Sq1 has a larger change rate (slope) of the heat generation characteristic than the second heat generation characteristic Sq2. That is, the temperature change due to heat generation is large. When the same excitation light is guided to the wavelength conversion member 65 and the light diffusing member 67, the temperature is changed with the rate of change of the combined heat generation characteristic Sqt obtained by adding the change rates of the first heat generation characteristic Sq1 and the second heat generation characteristic Sq2. To rise.

  However, when either the first optical fiber 59 or the second optical fiber 63 is disconnected, the rate of change in temperature is approximate to the slope of the first heat generation characteristic Sq1 or the slope of the second heat generation characteristic Sq2. Immediately after the occurrence of the disconnection, it does not become an approximate value, but it becomes a value close to the slope of Sq1 and Sq2 with the passage of time. Here, the slope of the first heat generation characteristic Sq1 is a first time change rate represented by ΔdT1 / Δdt1. In addition, the slope of the second heat generation characteristic Sq2 is a second time change rate represented by ΔdT2 / Δdt2. Therefore, when it is detected that the combined heat generation characteristic Sqt is either the first heat generation characteristic Sq1 or the second heat generation characteristic Sq2, the optical transmission generated in either the first optical fiber 59 or the second optical fiber 63 is detected. Loss (disconnection) can be determined using one temperature sensor 129.

  That is, when the detected value time change rate detected by the temperature sensor 129 matches the first time change rate, the endoscope control unit 127 determines that an optical transmission loss has occurred in the second optical fiber 63. When the detected value time change rate matches the second time change rate, the endoscope control unit 127 determines that an optical transmission loss has occurred in the first optical fiber 59.

  Here, the control content of each information is shown in a block diagram in FIG. The storage unit 135 stores, as data, a first time change rate 143 that is first temperature change rate information and a second time change rate 145 that is second temperature change rate information. In addition, the temperature sensor 129 outputs the detected value time change rate 149 of the temperature measurement value, which is the third temperature change rate information, to the endoscope control unit 127.

  The endoscope control unit 127 compares the detection value time change rate 149 output from the temperature sensor 129 with the first time change rate 143 and the second time change rate 145 stored in the storage unit 135, and It is determined whether an optical transmission loss has occurred in either the optical fiber 59 or the second optical fiber 63 (see FIG. 1). Since the detection value time change rate 149 changes sequentially, the endoscope control unit 127 repeatedly performs the above comparison / determination every predetermined time interval.

  In the above example, the rate of change of temperature with respect to time is used. However, not limited to time, for example, the rate of change of temperature for each temperature detection timing of the temperature sensor 129 or the rate of change of temperature for each timing at which a change in the light intensity instruction value occurs. Also good.

  FIG. 10 shows a state in which the target light amount of the laser light source that sequentially changes in accordance with the observation target and the temperature detection value from the temperature sensor 129 changes in accordance with the change in the target light amount. The target light amount is controlled to increase or decrease in accordance with the luminance information of the image signal output from the image sensor 49. The laser light source is driven according to the target light amount. When the first optical fiber 59 and the second optical fiber 63 are not disconnected, the temperature detection value from the temperature sensor 129 increases or decreases with a response delay with respect to the target light amount as indicated by the dotted line in the figure. However, when a break occurs in either the first optical fiber 59 or the second optical fiber 63, the temperature detection value is lower than when no break occurs, as indicated by the solid line in the figure. In addition, the responsiveness is delayed, and the rate of change in temperature with time decreases.

  Thus, the change in the detected temperature value has a clear difference depending on the presence or absence of disconnection. For this reason, even if it is measured by the temperature sensor 129 at an arbitrary timing, by comparing the obtained change of the temperature detection value with a predetermined reference value (analysis value when there is no disconnection), the optical fiber can be compared. The disconnection that occurs can be accurately detected at any time.

  The time change characteristics of the temperature of the wavelength conversion member 65 when there is no optical transmission loss such as disconnection can be analytically determined according to the types of the laser light source LD1, the laser light source LD2-A, and the laser light source LD2-B. Further, it can be analytically determined according to conditions such as output intensity of the light source and absorption / light emission characteristics according to the properties and types of the wavelength conversion member 65 and the light diffusion member 67.

  Therefore, in this configuration, the time change characteristics of the temperatures of the wavelength conversion member 65 and the light diffusion member 67 are analytically obtained and stored in the storage unit 135 in advance as temperature change information. Further, the time change rate of the temperature is stored in the storage unit 135 as a reference value at the normal time. Each temperature information to be stored may be the temperature of the wavelength conversion member 65 and the light diffusion member itself, or the temperature at the position of the temperature sensor 129. In the case of the temperatures of the wavelength conversion member 65 and the light diffusion member 67, when compared with the temperature detection value of the temperature sensor 129, an appropriate correction process may be performed as necessary.

  Returning to FIG. 7 again, the endoscope control unit 127 obtains the time change rate of the temperature detection value measured by the temperature sensor 129, and compares the obtained time change rate with the reference value stored in the storage unit 135 (St4). ). As a result of the comparison, if the rate of temperature change obtained by measurement is smaller than the reference value, it is determined that a break has occurred in either the first optical fiber 59 or the second optical fiber 63 (St5). If it is equal to the reference value, it is determined as normal and the optical transmission loss confirmation control mode is terminated.

  When it is determined that the disconnection has occurred, the endoscope control unit 127 outputs a control signal for turning off the laser light source to the light source control unit 75, and turns off the laser light source on the side where the disconnection has occurred (St6). As a result, it is possible to prevent the laser light source from being subjected to wasteful light amount control while maintaining normal exposure control.

  That is, in normal exposure control, the luminance information of the image signal output from the image sensor 49 is compared with an appropriate luminance level, and the output of the laser light source is controlled to increase or decrease depending on the excess or deficiency. When the disconnection occurs, the illumination light from the first illumination window 45 or the second illumination window 47 is insufficient, and the luminance of the imaging signal is lowered. Therefore, the target light amount of the laser light source is controlled to increase in order to set the decrease in luminance to an appropriate level. However, when disconnection occurs, even if the target light quantity is increased, the state where the illumination light is insufficient continues, and an illegal logic such as further increasing the target light quantity of the laser light source is caused. Therefore, when disconnection is detected, useless exposure control can be prevented by turning off the laser light source on the side where the disconnection has occurred.

  Next, the endoscope control unit 127 notifies the surgeon that a disconnection has occurred by displaying a message on the display unit 15 (St7). In addition to the display on the display unit 15, for example, notification may be performed by generating an alarm sound, or by lighting a lamp provided in the main body operation unit 23, the control device 13, or the like.

  As described above, in the endoscope apparatus 100, the endoscope control unit 127 detects the optical transmission loss at the rising timing of the drive signal. At the rising timing of the drive signal, the third temperature change rate based on the temperature measurement value is compared with the first temperature change rate and the second temperature change rate. Thereby, it is possible to make a highly accurate determination using the heat generation characteristics of the wavelength conversion member 65 and the light diffusion member 67. Further, the endoscope control unit 127 may start detecting the optical transmission loss at the timing when the pressing signal of the optical transmission loss confirmation button 33 provided in the endoscope 11 is received. In this case, since the optical transmission loss is detected at the rising timing of the drive signal after the button is pressed, the optical transmission loss can be detected at an arbitrary timing.

  In addition, in this configuration, since a single optical fiber is used, when the optical fiber is disconnected, the amount of illumination light is greatly reduced, and the optical transmission loss can be detected easily and reliably. For this reason, it becomes easy for the operator of the endoscope 11 to inspect the optical transmission loss before the endoscopic inspection.

Next, another configuration example of the endoscope apparatus 100 will be described.
FIG. 11 is a front view of an endoscope distal end portion 41 according to a modification in which two pairs of the first light source 69 and the third light source 157 are provided, and FIG. 12 is a configuration of the light source device 155 according to the modification shown in FIG. FIG.
In this modification, the light source device 155 includes two pairs of light sources each including a first light source 69 and a third light source 157. As described above, the first light source 69 includes a laser light source LD1 and a laser light source LD2-A. On the other hand, the third light source 157 includes a laser light source LD3 and a laser light source LD1. The laser light source LD3 is a blue-emitting semiconductor laser having a center wavelength of 473 nm. The laser light source LD3 and the light emitted from the laser light source LD1 are combined by a combiner 77. The combined outgoing light from the third light source 157 is introduced into the third optical fiber 159 that is the second light guide member 61 in which the light diffusion member 67 is disposed at the light outgoing end.

  The illumination light guided to the first optical fiber 59 is emitted from the first illumination window 45. The illumination light guided to the third optical fiber 159 is emitted from the third illumination window 161. The first illumination windows 45 and 45 are arranged on a straight line 165 sandwiching the observation window 43, and the third illumination windows 161 and 161 are arranged on a straight line 167 sandwiching the observation window 43. Thereby, white light and narrow-band light are evenly irradiated from both sides of the observation window 43 to prevent uneven illumination.

In the configuration according to this modification, observation with the following illumination light is possible by providing the third light source 157.
FIG. 13 shows the spectral characteristics of absorbance with respect to oxyhemoglobin and deoxyhemoglobin. As shown in the figure, both absorbances are equal in the vicinity of a wavelength of 405 nm, reduced hemoglobin has higher absorbance than oxyhemoglobin in the vicinity of wavelength 445 nm, and oxyhemoglobin has a higher absorbance than reduced hemoglobin in the vicinity of wavelength 473 nm. Further, the depth of penetration of the laser beam from the surface of the mucosal tissue has such a characteristic that it becomes shallower as the wavelength of the laser beam becomes shorter, so that the wavelengths become deeper in the order of 405 nm, 445 nm, and 473 nm.

Using these characteristics, the oxygen saturation of the observation region and the blood vessel depth projected in the observation region are obtained as follows.
(1) A captured image luminance value S1 obtained by detecting a return light component of the laser beam when irradiated with a laser beam having a central wavelength of 445 nm where the absorbance of reduced hemoglobin is high is obtained.
(2) A captured image luminance value S2 obtained by detecting a return light component of the laser beam when the laser beam having a central wavelength of 473 nm with high absorbance of oxyhemoglobin is irradiated is obtained.
(3) The brightness value of the picked-up image obtained by detecting the return light component of the laser light when the central wavelength 405 nm having the same absorbance is irradiated is obtained.
(4) The values of S1 and S2 are standardized with the value of S3, respectively. That is, the values of S1 / S3 and S2 / S3 are obtained.

(5) As shown in FIG. 14, a two-dimensional map in which the values of S1 / S3 and the magnitude of the values of S2 / S3 are represented by two orthogonal axes is generated, and the S1 obtained above is generated on this two-dimensional map. The values of / S3 and S2 / S3 are plotted. On the two-dimensional map, the greater the value of S1 / S3, the higher the oxygen saturation and the shallower the blood vessel depth, and the smaller the value of S1 / S3, the lower the oxygen saturation and the deeper the blood vessel depth. . Also, the greater the value of S2 / S3, the lower the oxygen saturation and the shallower the blood vessel depth, and the smaller the value of S2 / S3, the higher the oxygen saturation and the deeper the blood vessel depth. Based on these relationships, information on the level of oxygen saturation and blood vessel depth in the observation region is required.

  The present invention is not limited to the above-described embodiments, and those skilled in the art can change or apply the present invention based on the description of the specification and well-known techniques. included. For example, in the above configuration, the first light guide member 57 and the second light guide member 61 are single-line optical fibers, but the first light guide member 57 and the second light guide member 61 are not limited thereto. Even in the case of an optical fiber bundle in which a large number of optical fibers are bundled, the optical transmission loss can be detected in the same manner.

As described above, the following items are disclosed in this specification.
(1) An endoscope apparatus having a function of detecting optical transmission loss,
A first light source;
A first light guide member that introduces output light of the first light source and guides it to a distal end of an insertion portion that is inserted into a subject;
A wavelength conversion member disposed at a light exit end of the first light guide member;
A second light source;
A second light guide member for introducing the output light of the second light source and guiding the light to the tip of the insertion portion;
A light diffusing member disposed at a light exit end of the second light guide member;
Light source driving means for generating a drive signal corresponding to a target light amount set for each of the first light source and the second light source, and driving the first light source and the second light source;
A temperature sensor for detecting a temperature due to heat generated from the wavelength conversion member and the light diffusion member;
The first temperature change rate due to heat generation of the wavelength conversion member corresponding to the intensity of the drive signal of the first light source, and the second due to heat generation of the light diffusion member corresponding to the intensity of the drive signal of the second light source. Storage means for storing the temperature change rate of
A third temperature change rate of the temperature detected by the temperature sensor is compared with the first temperature change rate and the second temperature change rate, and the third temperature change rate is the first temperature. When the rate of change coincides with the second light guide member, it is determined that a light transmission loss has occurred. When the rate of change of the third temperature coincides with the rate of change of the second temperature, the first light guide member is determined. An optical transmission loss detecting means for determining that an optical transmission loss has occurred in the optical member;
An endoscopic apparatus comprising:
According to this endoscope apparatus, since the temperature of the wavelength conversion member and the light diffusing member rises due to light irradiation through the first light guide member and the second light guide member, It can be considered. The inclination of the temperature rise is larger in the wavelength conversion member. The temperature rising tendency of these two heating elements is detected by one temperature sensor in the vicinity. The slope of the temperature rise detected by the temperature sensor is compared with the first temperature change rate and the second temperature change rate, and is generated in either the first light guide member or the second light guide member. Optical transmission loss can be determined.

(2) The endoscope apparatus according to (1),
The endoscope apparatus in which the first temperature change rate, the second temperature change rate, and the third temperature change rate represent a temperature change rate with respect to time.
According to this endoscope apparatus, a change due to disconnection can be detected reliably and quickly by using the rate of change of temperature with respect to time.

(3) The endoscope apparatus according to (1) or (2),
An endoscope apparatus, wherein the temperature sensor is a single sensor disposed between the wavelength conversion member and the light diffusing member at a distal end of the insertion portion.
According to this endoscope apparatus, light transmission loss can be detected with a simple configuration, and the diameter of the endoscope can be reduced as compared with a configuration in which a temperature sensor is provided for each of the wavelength conversion member and the light diffusion member.

(4) The endoscope apparatus according to any one of (1) to (3),
An endoscope apparatus in which the first light source and the second light source are laser light sources, and each of the first light guide member and the second light guide member is a single optical fiber.
According to this endoscope apparatus, the optical transmission loss can be detected easily and reliably by using a single-line optical fiber that greatly reduces the amount of illumination light when a disconnection occurs. For this reason, it becomes easy for an endoscopic operator to perform an inspection of optical transmission loss before the endoscopic examination.

(5) The endoscope apparatus according to any one of (1) to (4),
An endoscope apparatus, wherein the wavelength conversion member is a phosphor that emits fluorescence when excited by output light from the first light source.
According to this endoscope apparatus, light of an arbitrary wavelength can be easily detected by using a phosphor.

(6) The endoscope apparatus according to (5),
An endoscope apparatus in which output light from the first light source and fluorescence from the phosphor are combined into white light.
According to this endoscope apparatus, color rendering can be improved by generating white light using fluorescence of a phosphor having a broad wavelength spectrum.

(7) The endoscope apparatus according to (6),
An endoscope apparatus in which the second light source is a light source that outputs narrow-band wavelength light having a spectrum different from that of white light.
According to this endoscope apparatus, wavelength light having a specific function can be selectively irradiated, and desired endoscopic observation can be performed with light having an appropriate wavelength according to the observation purpose.

(8) The endoscope apparatus according to (7),
An endoscope apparatus in which a center wavelength of the narrow-band wavelength light is 380 nm to 480 nm.
According to this endoscope apparatus, the fine structure of the capillary blood vessel on the tissue surface layer and the fine structure pattern of the mucosal tissue surface layer can be emphasized and observed.

(9) The endoscope apparatus according to any one of (1) to (8),
An endoscope apparatus in which the optical transmission loss detection means determines the optical transmission loss at a rising timing of the drive signal.
According to this endoscope apparatus, the third temperature change rate based on the temperature measurement value is compared with the first temperature change rate and the second temperature change rate at the rising timing of the drive signal. Compared with the falling timing of the drive signal, the heat generation characteristics of the wavelength conversion member and the light diffusing member can be used, and the determination can be made with high accuracy.

(10) The endoscope apparatus according to (9),
An endoscope apparatus that starts at a timing when the light transmission loss detecting means receives a press signal of a light transmission loss confirmation button provided on the endoscope.
According to this endoscope apparatus, since the optical transmission loss is detected at the rising timing of the drive signal after the button is pressed, the optical transmission loss can be detected at an arbitrary timing.

DESCRIPTION OF SYMBOLS 11 Endoscope 25 Insertion part 33 Optical transmission loss confirmation button 57 1st light guide member 59 1st optical fiber 61 2nd light guide member 63 2nd optical fiber 65 Wavelength conversion member 67 Light-diffusion member 69 1st light source 71 2nd light source 77 Light source control part (light source drive means)
127 Endoscope control unit (light transmission loss detection means)
129 Temperature sensor 135 Storage unit (storage means)
143 First time change rate (first temperature change rate)
145 Second time change rate (second temperature change rate)
149 Detection value time change rate (third temperature change rate)
100 Endoscopic devices LD1, LD2-A, LD2-B Laser light source

Claims (10)

An endoscope apparatus having a function of detecting optical transmission loss,
A first light source;
A first light guide member that introduces output light of the first light source and guides it to a distal end of an insertion portion that is inserted into a subject;
A wavelength conversion member disposed at a light exit end of the first light guide member;
A second light source;
A second light guide member for introducing the output light of the second light source and guiding the light to the tip of the insertion portion;
A light diffusing member disposed at a light exit end of the second light guide member;
Light source driving means for generating a drive signal corresponding to a target light amount set for each of the first light source and the second light source, and driving the first light source and the second light source;
A temperature sensor for detecting a temperature due to heat generated from the wavelength conversion member and the light diffusion member;
The first temperature change rate due to heat generation of the wavelength conversion member corresponding to the intensity of the drive signal of the first light source, and the second due to heat generation of the light diffusion member corresponding to the intensity of the drive signal of the second light source. Storage means for storing the temperature change rate of
A third temperature change rate of the temperature detected by the temperature sensor is compared with the first temperature change rate and the second temperature change rate, and the third temperature change rate is the first temperature. When the rate of change coincides with the second light guide member, it is determined that a light transmission loss has occurred. When the rate of change of the third temperature coincides with the rate of change of the second temperature, the first light guide member is determined. An optical transmission loss detecting means for determining that an optical transmission loss has occurred in the optical member;
An endoscopic apparatus comprising: The endoscope apparatus according to claim 1,
The endoscope apparatus in which the first temperature change rate, the second temperature change rate, and the third temperature change rate represent a temperature change rate with respect to time. The endoscope apparatus according to claim 1 or 2,
An endoscope apparatus, wherein the temperature sensor is a single sensor disposed between the wavelength conversion member and the light diffusing member at a distal end of the insertion portion. The endoscope apparatus according to any one of claims 1 to 3,
An endoscope apparatus in which the first light source and the second light source are laser light sources, and each of the first light guide member and the second light guide member is a single optical fiber. The endoscope apparatus according to any one of claims 1 to 4,
An endoscope apparatus, wherein the wavelength conversion member is a phosphor that emits fluorescence when excited by output light from the first light source. An endoscope apparatus according to claim 5, wherein
An endoscope apparatus in which output light from the first light source and fluorescence from the phosphor are combined into white light. The endoscope apparatus according to claim 6, wherein
An endoscope apparatus in which the second light source is a light source that outputs narrow-band wavelength light having a spectrum different from that of white light. The endoscope apparatus according to claim 7,
An endoscope apparatus in which a center wavelength of the narrow-band wavelength light is 380 nm to 480 nm. The endoscope apparatus according to any one of claims 1 to 8,
The optical transmission loss detecting means, the endoscope apparatus to determine the occurrence of the optical transmission loss at the rising edge of the drive signal. The endoscope apparatus according to claim 9, wherein
An endoscope apparatus in which the light transmission loss detection means starts determining the occurrence of the light transmission loss at a timing when a signal for pressing a light transmission loss confirmation button provided in the endoscope apparatus is received.

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