JP5789345B2 - Endoscope system - Google Patents

Description

  The present invention relates to an endoscope system that emphasizes and observes blood vessels on a living tissue.

  In recent medical treatments, diagnosis using an endoscope apparatus is widely performed. In this endoscopic diagnosis, special light observation using narrow-band light of a specific wavelength as illumination light has been performed in addition to normal light observation using broadband white light as illumination light in a subject. Yes.

  For special light observation, the surface and middle-deep blood vessels in the subject tissue are emphasized by irradiating the subject tissue with narrow-band light limited to the wavelength region where the absorption coefficient of blood hemoglobin is high in the blue and green wavelength regions. There is blood vessel enhancement observation to display. In this blood vessel enhancement observation, the blood vessel pattern is clarified by highlighting the superficial blood vessels, etc., so that it is easy to distinguish between cancer and diagnosis of the depth of cancer in the depth direction of the living tissue. .

  As the narrowband light used in the blood vessel enhancement observation, light obtained by narrowing a broadband light such as a xenon lamp with a bandpass filter has been used so far. Light mixed with laser light having a plurality of wavelengths emitted from a laser light source is also being used. In this Patent Document 1, light obtained by mixing two laser beams, a first laser beam having a center wavelength of 405 nm and a second laser beam having a center wavelength of 445 nm, and green to red fluorescence obtained by wavelength conversion of the second laser beam is used. By using the first laser beam and the second laser beam, the blood vessel enhancement observation is performed to emphasize the blood vessel of a predetermined depth by adjusting the light amount ratio between the first laser beam and the second laser beam.

JP 2011-10998 A

  In Patent Document 1, since the first and second laser beams are also irradiated in combination with the fluorescent light having a broad band wavelength, the blood vessel is in a very bright state as compared with the case where only the light having a narrow band of xenon light is used. Emphasis observation is possible. However, since the laser light has higher luminance than fluorescence, it is easy to capture various changes in the living tissue. For example, a laser beam having a wavelength range in which the magnitude relationship between the absorption coefficients of oxyhemoglobin and reduced hemoglobin is not switched (that is, a wavelength range in which the magnitude relationship between the absorption coefficients of oxidized and reduced hemoglobin is always the same) is used. In some cases, the appearance of the blood vessel pattern varies greatly depending on the change in the oxygen saturation of blood hemoglobin. If the appearance of the blood vessel pattern changes in this way, it may happen that cancer differentiation and depth of diagnosis cannot be performed reliably. That is, there are cases where robustness cannot be maintained with respect to the appearance of the blood vessel pattern.

  An object of the present invention is to provide an endoscope system that does not change the appearance of a blood vessel pattern even when the oxygen saturation of blood hemoglobin changes.

The endoscope system of the present invention emits second illumination light that sandwiches an isosbestic wavelength of oxidized and reduced hemoglobin between a first semiconductor light source that emits first illumination light and the wavelength of the first illumination light. 2 a semiconductor light source, a light source control unit that simultaneously irradiates a subject tissue from the same illumination window with the first illumination light and the second illumination light within one frame period, and the first illumination light and the second illumination light. Complementary color image pickup means for picking up the return light from the illuminated subject tissue, and image generation means for generating a blood vessel enhancement image based on an image signal obtained by the complementary color image pickup means, and blood vessel enhancement In the image, the blood vessel of the subject tissue is displayed in a pseudo color by the image generating means, or in at least one of the subject tissue or the blood vessel-enhanced image, the blood vessel contrast between the blood vessel and the other part is a contrast adjusting hand. Characterized in that it is adjusted by.

  A mode switching unit for switching between a plurality of modes including a special mode for displaying a blood vessel-enhanced image is provided, and a light amount ratio between the first illumination light and the second illumination light is different in a mode other than the special mode and the special mode. Preferably it is.

  The contrast adjusting means is preferably a light amount ratio adjusting unit that adjusts the blood vessel contrast by adjusting the light amount ratio between the first illumination light and the second illumination light. The contrast adjusting means is preferably a density conversion processing unit that adjusts the blood vessel contrast by performing density conversion processing on the blood vessel emphasized image.

  It is preferable that the first illumination light and the second illumination light have the same absolute value of the difference in extinction coefficient between oxidized and reduced hemoglobin. A wavelength range of the first illumination light includes a third semiconductor light source that irradiates the subject tissue with third illumination light having a wavelength different from that of the first illumination light and the second illumination light and having the same light absorption characteristics as the second illumination light. The absolute value Dx of the difference in the extinction coefficient between the oxidized and reduced hemoglobin in the wavelength range of the second illumination light is the absolute value Dy1 of the difference in the extinction coefficient of the oxidized and reduced hemoglobin and the oxidized and reduced hemoglobin in the wavelength range of the third illumination light. It is preferably substantially equal to the sum of the absolute values Dy2 of the difference in extinction coefficients.

  According to the present invention, the subject tissue is illuminated with the first and second illumination light sandwiching the equal absorption wavelength of oxidized and deoxyhemoglobin between the wavelengths, and the blood vessel obtained by imaging the subject tissue or the subject tissue. Since the blood vessel contrast between the blood vessel and the other portion is adjusted in at least one of the emphasized images, the appearance of the blood vessel pattern does not change even if the oxygen saturation of blood hemoglobin changes ( That is, robustness can be maintained with respect to the appearance of blood vessels.)

It is a figure which shows the external appearance of an endoscope system. It is a figure which shows the functional structure of an endoscope system. It is a figure which shows the light emission pattern at the time of normal mode. It is a graph which shows the extinction coefficient of oxygenated hemoglobin HbO2 and reduced hemoglobin Hb. It is a figure which shows an image in the case of oxygen saturation (StO2) 100%, 50%, and 0% in 1st special mode. It is a figure for demonstrating the blood vessel contrast when AE act | operates. It is a figure which shows the light emission pattern at the time of 2nd special mode. It is a figure which shows an image in the case of oxygen saturation (StO2) 100%, 50%, and 0% in 2nd special mode. It is a figure which shows the light emission pattern at the time of 3rd special mode. It is a figure which shows an image in the case of oxygen saturation (StO2) 100%, 50%, and 0% in a 3rd special mode. It is a figure which shows the light emission pattern at the time of oxygen saturation mode. It is a figure which shows an image in oxygen saturation (StO2) 100%, 50%, and 0% in oxygen saturation mode. It is a graph which shows the permeation | transmission characteristic of the color filter of B, G, R of CCD. It is a figure for demonstrating the imaging control of CCD in the normal mode. It is a figure for demonstrating the imaging control of CCD in the 1st-3rd special mode and oxygen saturation mode. It is a figure which shows each part of a special image generation part. It is a figure for demonstrating the blood vessel contrast. It is a figure for demonstrating the reference | standard contrast in a 2nd special mode. It is a figure for demonstrating the reference | standard contrast in a 3rd special mode. It is a figure for demonstrating light quantity ratio fine adjustment. It is a figure for demonstrating a light / dark conversion process. It is a flowchart showing a series of flows in the second special mode. It is a figure for demonstrating the blood vessel emphasis at the time of using 3 wavelength narrow-band light.

  As shown in FIG. 1, an endoscope system 10 includes an electronic endoscope 11 that images an inside of a subject, a processor device 12 that performs various image processing on an image captured by the electronic endoscope 11, and a subject. A light source device 13 that supplies light to be radiated to the electronic endoscope 11 and a monitor 14 that displays an image subjected to various image processes by the processor device 12 are provided.

  The electronic endoscope 11 includes a flexible insertion portion 16 to be inserted into a subject, an operation portion 17 provided at a proximal end portion of the insertion portion 16, an operation portion 17, a processor device 12, and a light source device 13. And a universal cord 18 for connecting the two. A bending portion 19 in which a plurality of bending pieces are connected is formed at the distal end of the insertion portion 16. The bending portion 19 is bent in the vertical and horizontal directions by operating the angle knob 21 of the operation portion 17. At the distal end of the bending portion 19, a distal end portion 16a incorporating an optical system for in-vivo imaging is provided. The distal end portion 16 a is directed in a desired direction within the subject by the bending operation of the bending portion 19.

  Further, the operation unit 17 is provided with a mode switching SW 15 for switching to various modes. Various modes include normal mode for observing a subject illuminated with broadband white light, and observation with a constant blood vessel contrast (blood vessel and mucous membrane contrast) regardless of changes in oxygen saturation of blood hemoglobin. A first special mode for enhancing a blood vessel on the living tissue, a second special mode for emphasizing the blood vessel on the living tissue by pseudo color display, and a second mode for enhancing the blood vessel on the living tissue while maintaining the brightness of the subject. There are a total of four modes: three special modes and an oxygen saturation mode for observing the oxygen saturation of blood hemoglobin.

  A connector 24 is attached to the universal cord 18 on the processor device 12 and the light source device 13 side. The connector 24 is a composite type connector including a communication connector and a light source connector, and the electronic endoscope 11 is detachably connected to the processor device 12 and the light source device 13 via the connector 24.

  As shown in FIG. 2, the light source device 13 is a light source control that controls the driving of the laser light sources LD1 and LD2, the phosphor 30, the first optical fiber 32, the second optical fiber 33, and the laser light sources LD1 and LD2. A portion 35 is provided. The laser light sources LD1 and LD2 are constituted by semiconductor light sources such as laser diodes. The laser light source LD1 emits blue narrow band light BN1 of 445 nm ± 10 nm, and the laser light source LD2 emits blue narrow band light BN2 of 405 ± 10 nm. The blue narrow band light BN1 is applied to the phosphor 30 provided between the laser light source LD1 and the first optical fiber 32, and the blue narrow band light BN2 is passed through the condensing lens 33a. Is incident on. As a semiconductor light source, an LED (Light Emitting Diode) may be used instead of the laser light sources LD1 and LD2.

The phosphor 30 contains a plurality of types of fluorescent materials (for example, YAG-based fluorescent materials or fluorescent materials such as BAM (BaMgAl ₁₀ O ₁₇ )). In the phosphor 30, most of the blue narrow-band light from the laser light source LD1 is absorbed by a plurality of fluorescent materials to excite and emit green to red (460 to 700 nm) fluorescence FL, and the rest is transmitted as it is. Therefore, the phosphor 30 emits white light W in which the blue narrow band light BN and the fluorescence FL are mixed. The white light W is incident on the first optical fiber 32 through the condenser lens 32a.

  The first optical fiber 32 and the second optical fiber 33 are connected to a light guide 43 in the electronic endoscope by a coupler 36. As a result, the white light W from the first optical fiber 32 and the blue narrow-band light BN2 from the second optical fiber 33 are incident on the light guide 43 selectively or simultaneously.

  The light source control unit 35 is connected to a controller 59 in the processor device, and controls the light amounts of the laser light sources LD1 and LD2 to be turned on (turned on) and off (lighted off) according to the mode. When the normal mode is set, only the laser light source LD1 is always turned on. Thereby, as shown in FIG. 3, only the white light W is always irradiated to the subject.

  On the other hand, when the first to third special modes and the oxygen saturation mode are set, the laser light sources LD1 and LD2 are turned on. As a result, as shown in FIGS. 6A, 7A, and 8, the subject is irradiated with mixed light of white light W (blue narrowband light BN1 + fluorescence FL) and blue narrowband light BN2. The light quantity ratio between the blue narrow band light BN1 and the blue narrow band light BN2 is predetermined for each mode, and the light quantity ratio of each mode is stored in the light quantity ratio storage unit 35a in the light source control unit.

  When the first special mode is set, the blue narrow band lights BN1 and BN2 are emitted at a predetermined first light quantity ratio. When light is emitted at this first light quantity ratio, as shown in FIG. 4, light having a wavelength range including the blue narrow-band light BN2 having a center wavelength of 405 nm and having a larger extinction coefficient of oxidized hemoglobin HbO2 than the extinction coefficient of reduced hemoglobin Hb ( Light having a first different absorption wavelength) and light having a light absorption coefficient of reduced hemoglobin Hb that includes blue narrow-band light BN1 having a central wavelength of 445 nm (light having a second different absorption wavelength) that is greater than that of oxidized hemoglobin HbO2. The object is irradiated with substantially the same amount of light. It should be noted that an isosbestic wavelength having the same extinction coefficient of oxidized and reduced hemoglobin is sandwiched between the wavelength bands of the blue narrow band lights BN1 and BN2.

  In the case of the first special mode, as shown in FIG. 5A, when the oxygen saturation is 100%, the blood vessel and the mucosa have the same blood vessel contrast in both cases of 50% and 0%. That is, in the first special mode, blood vessels can be observed with the same blood vessel contrast regardless of the change in the oxygen saturation StO2. This blood vessel contrast does not change even when AE (Auto Exposure) is activated and the total light amount (the total light amount of the blue narrow-band light BN1, BN2 and the fluorescence FL) changes.

  For example, as shown in FIG. 5B, when the distal end portion 16a of the electronic endoscope is brought close to the subject tissue and becomes bright overall (in the foreground state), AE for reducing the total light amount is performed. At this time, although the brightness of the blood vessel is darkened by AE, the brightness of the mucous membrane is also darkened accordingly, so that the blood vessel contrast does not change before and after AE. The same applies to the first to third special modes and the oxygen saturation mode. In FIG. 5, the luminance values of blood vessels and mucous membranes are evaluated in 10 levels. “10” is the brightest, “10” to “1” gradually becomes dark, and “1” is the darkest. Show. The same applies to the following.

  When the second special mode is set, as shown in FIG. 6A, each narrowband light has a second light quantity ratio in which the light quantity L2 of the blue narrowband light BN2 is larger than the light quantity L1 of the blue narrowband light BN1. Is emitted. In this case, the light amount of the first different absorption wavelength light (HbO2> Hb) including the blue narrow band light BN1 having the center wavelength of 405 nm is larger than the light amount of the second different absorption wavelength light (Hb> HbO2). . Therefore, as shown in FIG. 6B, the blood vessel brightness becomes brighter as the oxygen saturation becomes 100%, 50%, and 0% (assuming that the AE is not activated), so that the blood vessel contrast is increased. Also changes. This change in blood vessel contrast is corrected by the light amount ratio fine adjustment unit 62 or the light / dark conversion processing unit 63.

  When the third special mode is set, as shown in FIG. 7A, each narrowband light has a third light quantity ratio in which the light quantity L1 of the blue narrowband light BN1 is larger than the light quantity L2 of the blue narrowband light BN2. Is emitted. In this case, the total amount of light of the second different absorption wavelength (Hb> HbO2) including the blue narrow band light BN1 having the center wavelength of 445 nm is larger than the total amount of light of the first different absorption wavelength light (HbO2> Hb). growing. Therefore, as shown in FIG. 7B, as the oxygen saturation becomes 100%, 50%, 0% and the hypoxic state, the brightness of the blood vessel becomes darker (assuming that the AE is not activated), and thus the blood vessel contrast. Also changes. This change in blood vessel contrast is corrected by the light amount ratio fine adjustment unit 62 or the density conversion processing unit 63 as in the second special mode.

  When the oxygen saturation mode is set, as shown in FIG. 8A, the light amount L2 of the blue narrow band light BN2 is substantially larger than the light amount L1 of the blue narrow band light BN1, Narrow band light is emitted. In this case, the total amount of light of the first different absorption wavelength (HbO2> Hb) including the blue narrow band light BN2 having the center wavelength of 405 nm is larger than the total amount of light of the second different absorption wavelength (Hb> HbO2). , Get pretty big. Therefore, as shown in FIG. 8B, the blood vessel brightness changes greatly as the oxygen saturation level becomes 100%, 50%, and 0% (assuming that AE is not activated). In the oxygen saturation mode, changes in the oxygen saturation image are imaged using changes in the brightness of the blood vessels.

  As shown in FIG. 2, the electronic endoscope 11 includes a light guide 43, a CCD 44, an analog processing circuit 45 (AFE: Analog Front End), and an imaging control unit 46. The light guide 43 is a large-diameter optical fiber, a bundle fiber, or the like, the incident end is connected to the light source device 13, and the emission end is directed to the irradiation lens 48. The light guided in the light guide 43 is irradiated into the subject through the irradiation lens 48 and the illumination window 49.

  The observation window 50 receives return light from the subject. The received light is incident on the CCD 44 through the imaging lens 51. The CCD 44 has an image pickup surface 44a on which light from the imaging lens 51 is incident. The light received by the image pickup surface 44a is photoelectrically converted to accumulate signal charges. The accumulated signal charge is read as an imaging signal and sent to the AFE 45.

  The CCD 44 is a color CCD, and on the imaging surface 44a, there are 3 pixels: a B pixel provided with a B color filter, a G pixel provided with a G color filter, and an R pixel provided with an R color filter. Color pixels are arranged. These color filters of B color, G color, and R color have spectral transmittances indicated by transmission curves 52, 53, and 54 shown in FIG. Therefore, the B pixel receives light of 380 to 560 nm, the G pixel receives light of 450 to 630 nm, and the R pixel receives light of 580 to 760 nm. In place of the CCD, a CMOS provided with an RGB color filter may be used. In place of the RGB color filters, a CCD or CMOS provided with complementary CMY color filters may be used.

  The AFE 45 includes a correlated double sampling circuit (CDS), an automatic gain control circuit (AGC), and an analog / digital converter (A / D) (all not shown). The CDS performs correlated double sampling processing on the image pickup signal from the CCD 44 to remove noise generated by driving the CCD 44. The AGC amplifies the imaging signal from which noise has been removed by CDS. The A / D converts the imaging signal amplified by the AGC into a digital imaging signal having a predetermined number of bits and inputs the digital imaging signal to the processor device 12.

  The imaging control unit 46 is connected to a controller 59 in the processor device 12, and sends a drive signal to the CCD 44 when an instruction is given from the controller 59. The CCD 44 outputs an imaging signal to the AFE 45 at a predetermined frame rate based on the drive signal from the imaging control unit 46.

  When the normal observation mode is set, as shown in FIG. 10A, in one frame period, white light W (blue narrowband light BN1 + fluorescence FL) is photoelectrically converted and signal charges are accumulated; A step of reading out the accumulated signal charge is performed. This imaging control is repeatedly performed while the normal observation mode is set. Thereby, from the B pixel, G pixel, and R pixel of the CCD 44, the blue signal Bc, the green signal Gc, and the red signal Rc are read out as the imaging signals, respectively.

  On the other hand, when the first to third special modes and the oxygen saturation mode are set, as shown in FIG. 10B, the white light W (blue narrowband light BN1 + fluorescence FL) and the blue light within one frame period. A step of photoelectrically converting the mixed color light of the narrow-band light BN2 to accumulate signal charges and a step of reading out the accumulated signal charges are performed. Thereby, from the B pixel, G pixel, and R pixel of the CCD 44, the blue signal Bs, the green signal Gs, and the red signal Rs are read out as imaging signals, respectively.

  As shown in FIG. 2, the processor device 12 includes a normal image generation unit 55, a frame memory 56, a special image generation unit 57, and a display control circuit 58, and a controller 59 controls each unit. The normal image generation unit 55 generates a normal image from the imaging signals Bc, Gc, and Rc obtained in the normal mode. The B image, the G image, and the R image of the normal image are assigned to the B, G, and R channels of the monitor 14, respectively. The normal image is temporarily stored in the frame memory 56 before being displayed on the monitor 14.

  As shown in FIG. 11, the special image generation unit 57 generates a blood vessel enhancement image generation unit 60 that generates a blood vessel enhancement image in which blood vessels on a biological tissue are emphasized from the imaging signals obtained in the first to third special modes. An oxygen saturation image generation unit 71 that generates an oxygen saturation image obtained by imaging oxygen saturation from an imaging signal obtained in the oxygen saturation mode. The blood vessel enhancement image generation unit 60 is configured to determine whether or not the blood vessel contrast matches the reference contrast. The blood vessel contrast determination unit 61 corrects the blood vessel contrast by finely adjusting the second and third light amount ratios. It is characterized by comprising an adjustment unit 62, a density conversion processing unit 63 that converts the density of blood vessels and corrects the blood vessel contrast, and an image generation unit 64 that generates a blood vessel emphasized image.

  The blood vessel contrast determination unit 61 generates a B / G ratio image indicating the luminance ratio between the blue signal Bs and the green signal Gs based on the blue signals Bs and Gs obtained in the second and third special modes. In this B / G ratio image, a pixel region having a B / G ratio within a certain range is identified as a mucous membrane, and a pixel region having a B / G ratio outside the certain range is identified as a blood vessel. When the blood vessel and the mucous membrane are specified, as shown in FIG. 12, the ratio (X: Y) of the luminance value X of the blood vessel and the luminance value Y of the mucous membrane is calculated as the blood vessel contrast. Then, it is determined whether or not the calculated blood vessel contrast has reached the reference contrast.

  The reference contrast is the blood vessel contrast when the oxygen saturation is 100%. In the second special mode of the present embodiment, the brightness of the blood vessel is the darkest when the oxygen saturation is 100%, and the brightness of the blood vessel becomes brighter as the hypoxic state is reached. Therefore, as shown in FIG. 13A, when the blood vessel luminance value at the oxygen saturation of 100% is “2” and the mucosal luminance value is “8”, the reference contrast is “1: 4”. .

  On the other hand, in the third special mode, the brightness of the blood vessel is the brightest when the oxygen saturation is 100%, and the brightness of the blood vessel becomes darker as the hypoxic state is reached. Therefore, when the blood vessel luminance value is “6” and the mucosal luminance value is “8” when the oxygen saturation is 100%, the reference contrast is “2: 3” as shown in FIG. 13B. . When observing a site with many arteries, it is preferable to use the blood vessel contrast when the oxygen saturation is 100% as the reference contrast. However, when observing a site with many veins, the oxygen saturation The blood vessel contrast at 70% is preferably used as the reference contrast.

  As shown in FIG. 14, the light amount ratio fine adjustment unit 62 finely adjusts the second and third light amount ratios to correct the blood vessel contrast when the blood vessel contrast does not reach the reference contrast. In the second special mode, the total light amount of the first different absorption wavelength including the blue narrow band light BN2 having the center wavelength of 405 nm is larger than the total light amount of the second different absorption wavelength including the blue narrow band BN1 having the center wavelength of 445 nm. When the blood vessel becomes brighter due to a decrease in oxygen saturation, the blood vessel contrast does not match the reference contrast.

  Therefore, the light amount ratio fine adjustment unit 62 drives the light source control unit 35 of the light source device to decrease the light amount of the blue narrow band light BN2 and reduce the light amount of the first different absorption wavelength, while reducing the blue narrow band light BN1. Is increased to increase the amount of light at the second different absorption wavelength. Thereby, the second light quantity ratio is finely adjusted, and the brightness of the blood vessel becomes dark like when the oxygen saturation is 100%. Further, when the color tone of the mucous membrane changes with the fine adjustment of the second light quantity ratio, the color tone of the mucous membrane is also adjusted. As a result, the blood vessel contrast matches the reference contrast. Even in the third special mode, the third light quantity ratio is finely adjusted in the same procedure as described above.

  As shown in FIG. 15, the light / dark conversion processing unit 63 converts the light / dark of the blood vessel and corrects the blood vessel contrast when the blood vessel contrast does not reach the reference contrast. In the second special mode, as described above, when the brightness of the blood vessel becomes bright due to the decrease in oxygen saturation, the blood vessel contrast does not match the reference contrast. In this case, the light / dark conversion processing unit 63 generates a blood vessel image in which only blood vessels are imaged and a mucosal image in which mucous membranes other than blood vessels are imaged, from the imaging signal obtained in the second special mode. The blood vessel image is generated by extracting a blood vessel region in which the signal ratio (B / G ratio) between the blue signal Bs and the green signal Gs is outside a certain range from the imaging signal. The mucous membrane image is generated by extracting a mucosal region where the B / G ratio is within a certain range.

  Then, the light / dark conversion processing unit 63 performs light / dark conversion processing on the blood vessel image to change the blood vessel luminance value “4” to the luminance value “2” when the oxygen saturation is 100%. Then, the blood vessel image and the mucous membrane image subjected to the density conversion process are synthesized. Thereby, an image in which the blood vessel contrast matches the reference contrast is obtained. In the case of the third special mode, the light / dark conversion process is performed in the same procedure as described above.

  When the first special mode is set, the image generation unit 64 generates a first blood vessel emphasized image based on the blue signal Bs, the green signal Gs, and the red signal Rs obtained by the electronic endoscope 11. To do. The B image, G image, and R image of the first blood vessel enhanced image are assigned to the B, G, and R channels of the monitor 14, respectively. As shown in FIG. 5A, since the blood vessel contrast is constant in the first blood vessel-enhanced image even when a change in oxygen saturation occurs, the appearance of blood vessels does not change. Note that the first blood vessel emphasized image is temporarily stored in the frame memory 56 before being displayed on the monitor 14. The same applies to the following second and third blood vessel emphasized images.

  In addition, when the second special mode is set, the image generation unit 64 performs the blue signal Bs, the green signal Gs, or the light / dark conversion process obtained under the second light amount ratio after fine adjustment. Based on the blue signal Bs and the green signal Gs, the second blood vessel enhanced image is generated. The B image of the second blood vessel enhanced image is assigned to the B and G channels of the monitor 14, and the G image is assigned to the R channel of the monitor 14. Thereby, in the second blood vessel emphasized image, the entire subject image including the blood vessel is displayed in a pseudo color.

  Further, when the third special mode is set, the image generation unit 64 has the blue signal Bs, the green signal Gs, the red signal Rs, or the light and shade obtained under the third light amount ratio after fine adjustment. A third blood vessel enhanced image is generated based on the blue signal Bs, green signal Gs, and red signal Rs that have been subjected to the conversion process. The B image, G image, and R image of the third blood vessel emphasized image are assigned to the B, G, and R channels of the monitor 14, respectively. As a result, in the third blood vessel enhanced image, the blood vessel image is emphasized and displayed on the biological tissue having a color with a certain brightness or higher.

  The oxygen saturation image generation unit 71 includes a correlation storage unit (not shown) that stores in advance the correlation between the blue signal Bs, the green signal Gs, the red signal Rs, and the oxygen saturation. From this correlation storage unit, the oxygen saturation corresponding to each pixel of the blue signal Bs, the green signal Gs, and the red signal Rs obtained in the oxygen saturation mode is obtained. An oxygen saturation image is generated based on the obtained oxygen saturation. As the oxygen saturation image, in addition to a complete pseudo color image that is displayed by assigning different colors according to the oxygen saturation, only a low oxygen region where the oxygen saturation is below a certain value is displayed in pseudo color, and the other images are normal images. A partial pseudo color image displayed with the same color can be considered.

  Next, the flow of processing in the second special mode will be described using the flowchart of FIG. In the third special mode, the procedure is substantially the same as that in the second special mode, and a description thereof will be omitted. When the second special mode is set, the blue narrowband light BN2 has a second light quantity ratio (405> 445) in which the light quantity of the blue narrowband light BN2 is larger than the light quantity of the blue narrowband light BN1, and the blue narrowband light BN1, BN2, and the fluorescence FL The mixed color light is irradiated to the subject. By imaging this subject with the color CCD 44, a blue signal Bs, a green signal Gs, and a red signal Rs for three colors are obtained.

  The blood vessel contrast between the blood vessel and the mucous membrane is detected from the blue signal Bs, green signal Gs, and red signal Rs for these three colors. When the blood vessel contrast matches a predetermined reference contrast, a second blood vessel enhanced image is generated based on the blue signal Bs, the green signal Gs, and the red signal Rs. On the other hand, when the blood vessel contrast does not match the reference contrast, the second light quantity ratio is finely adjusted so as to match the reference contrast. In this fine adjustment of the second light amount ratio, the total light amount (total light amount of the mixed light of blue narrow band light BN1, BN2 and fluorescence FL) is kept constant while the light amount of blue narrow band light BN2 is reduced. The amount of blue narrow band light BN1 is increased. When the color tone of the mucous membrane is changed by fine adjustment of the second light quantity ratio, the color tone is returned to the color tone of the mucous membrane before fine adjustment. Then, a second blood vessel enhanced image is generated based on the blue signal Bs, the green signal Gs, and the red signal Rs acquired after fine adjustment of the second light quantity ratio. The generated second blood vessel emphasized image is displayed on the monitor 14.

  In the above embodiment, in the first special mode, by setting the light amount ratio of the two wavelengths of blue narrowband light BN1 and BN2 sandwiching the equal absorption wavelength to a predetermined value, regardless of the change in the oxygen saturation StO2, Although the blood vessel contrast is kept constant, use two narrowband light with the same absolute value of the difference between the absorption coefficients of oxidized and reduced hemoglobin with the same absorption wavelength, or with the same absorption wavelength. In addition to the narrowband light, the blood vessel contrast may be made constant by adding another wavelength of narrowband light.

  For example, as shown in FIG. 17, in the case where the subject is simultaneously irradiated with narrow-band light having two wavelengths S1 and S2 having different absorption characteristics of oxidized and reduced hemoglobin, the difference between the absorption coefficients of oxidized and reduced hemoglobin at the wavelength S1. Since the absolute value Dx exceeds the absolute value Dy1 of the difference between the extinction coefficients of the oxidized and reduced hemoglobin at the wavelength S2, unless the light quantity ratio is set appropriately, if there is a change in the oxygen saturation StO2, The contrast cannot be kept constant. Therefore, in addition to the narrowband light of the two wavelengths S1 and S2, narrowband light of the wavelength S3 having the same absorption characteristics (HbO2> Hb) as the wavelength S2 (the absolute value of the difference between the extinction coefficients of oxidized and reduced hemoglobin is Dy2 ) To achieve Dx = Dy1 + Dy2. Thereby, even if the oxygen saturation StO2 changes, the blood vessel contrast can be kept constant.

  In the above embodiment, the two wavelengths of blue narrowband light BN1 and BN2 sandwiching the equal absorption wavelength are simultaneously irradiated. However, the two wavelengths of blue narrowband light BN1 and BN2 are sequentially irradiated, and the reflected images are sequentially captured. May be. The image of the blue narrowband light BN1 and the image of the blue narrowband light BN2 obtained by this imaging are combined with each other, and image processing for making the blood vessel contrast constant is performed on the combined image.

  In the above embodiment, the blood vessel contrast is made constant by adjusting the color of the mucous membrane after fine adjustment of the second light quantity ratio. Instead, the image obtained after fine adjustment of the second light quantity ratio is displayed. On the other hand, the blood vessel contrast may be made constant by performing not only blood vessels but also mucous membrane density conversion processing.

DESCRIPTION OF SYMBOLS 10 Endoscope system 15 Mode switching means 35 Light source control part 57 Special image generation part 62 Light quantity ratio fine adjustment part 63 Contrast conversion process part 64 Blood vessel emphasis image generation part 71 Oxygen saturation image generation part LD1, LD2 Laser light source

Claims (6)

A first semiconductor light source that emits first illumination light;
A second semiconductor light source that emits a second illumination light that sandwiches an isosbestic wavelength of oxidized and reduced hemoglobin between the wavelength of the first illumination light; and
A light source controller that simultaneously irradiates the subject tissue from the same illumination window within one frame period with the first illumination light and the second illumination light;
A complementary color imaging device that images the return light from the subject tissue illuminated by the first illumination light and the second illumination light;
Image generating means for generating a blood vessel emphasized image based on the image signal obtained by the complementary color imaging means;
In the blood vessel emphasized image, the blood vessel of the subject tissue is displayed in a pseudo color by the image generation unit, or at least one of the subject tissue or the blood vessel emphasized image is a blood vessel contrast between the blood vessel and the other portion. Is adjusted by a contrast adjusting means. A mode switching unit for switching between a plurality of modes including a special mode for displaying the blood vessel emphasized image;
The first light amount ratio of the illumination light second illumination light, an endoscope system of the special mode and said that according to claim 1, wherein different in mode other than the special mode. The contrast adjustment means, by adjusting the light amount ratio of the first illumination light and the second illumination light, the endoscope according to claim 1 or 2, wherein said a light intensity ratio adjustment unit for adjusting the blood vessel contrast system. The contrast adjustment means, said by shading conversion processing vessel emphasized image, the endoscope system according to claim 1 or 2, wherein the a gray conversion processing unit for adjusting the blood vessel contrast. The endoscope system according to any one of claims 1 to 4, wherein the first illumination light and the second illumination light have the same absolute value of a difference in extinction coefficient between oxidized and reduced hemoglobin. A third semiconductor light source that irradiates a subject tissue with a third illumination light having a wavelength different from that of the first illumination light and the second illumination light and having a light absorption characteristic similar to that of the second illumination light;
The absolute value Dx of the difference between the extinction coefficients of the oxidized and reduced hemoglobin in the wavelength range of the first illumination light is the absolute value Dy1 of the difference between the extinction coefficients of the oxidized and reduced hemoglobin in the wavelength range of the second illumination light. The endoscope system according to any one of claims 1 to 4 , wherein the endoscope system is substantially equal to a value obtained by adding an absolute value Dy2 of a difference between the extinction coefficients of oxidized and reduced hemoglobin in a wavelength region of illumination light.

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