JP2010268961A - Medical observation system - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a medical observation system suitable for carrying out processing of an abnormal image, such as over exposure or under exposure. <P>SOLUTION: The medical observation system includes means for scanning an object by light from a predetermined light source, means for detecting an image signal by receiving reflection of the scanned light, means for determining the pixel arrangement of image information expressed by each image signal on the basis of detection timing of each image signal, means for generating an image by spatially arranging each piece of image information in accordance with the determined pixel arrangement, means for detecting an intensity value of an image signal detected at a timing according to each pixel, means for deciding, when the detected intensity value is equal to or larger than a first threshold or equal to or smaller than a second threshold, a pixel corresponding to the detected intensity value as an abnormal pixel, and means for carrying out a predetermined processing on the decided abnormal pixel on a pixel unit basis. <P>COPYRIGHT: (C)2011,JPO&INPIT

Description

  The present invention relates to a medical observation system that scans an observation target to generate an observation image, and more specifically, scans that acquire image information by optically scanning an object by resonating the tip of an ultrafine optical fiber. The present invention relates to a medical observation system having a type medical probe.

  An electronic scope is generally known as a medical device used when a doctor observes a body cavity of a patient. A doctor who uses the electronic scope inserts the insertion portion of the electronic scope into the body cavity and guides the distal end portion provided at the distal end of the insertion portion to the vicinity of the observation target. A doctor operates an operation unit of an electronic scope or a video processor as necessary in order to take an image of the inside of a body cavity with a solid-state imaging device such as a CCD (Charge Coupled Device) mounted on the tip. A doctor observes an image in a body cavity obtained as a result of various operations through a monitor, and performs examinations and treatments.

  As described above, the electronic scope is used by being inserted into a body cavity of a patient. Therefore, regarding electronic scopes, there is a constant demand for reducing the diameter of the insertion portion in order to reduce the burden on the patient. In order to reduce the diameter of the electronic scope, it is desired to reduce the size of the various built-in components themselves in addition to devising the arrangement of the various built-in components. In addition to the solid-state image sensor, the electronic scope includes a large number of components such as a peripheral circuit of the solid-state image sensor, a shield member, an insulating member, an objective lens, an illumination lens, a lens holding frame, and an optical fiber bundle.

  Among the built-in parts of electronic scopes, solid-state imaging devices and optical fiber bundles have particularly large external dimensions. In addition, the minimum size that can be designed for other components such as an objective lens and an illumination lens is defined by the effective pixel area of the solid-state imaging device, the outer dimensions of the optical fiber bundle, and the like. Therefore, when a small solid-state imaging device or a thin optical fiber bundle is adopted, it is easy to design a thin electronic scope. However, in general, the smaller the solid-state image sensor, the more difficult it is to satisfy desired performance with respect to various parameters such as resolution, dynamic range, and SN ratio. Further, when the diameter of the optical fiber bundle is reduced, that is, when the number of optical fibers is reduced, there arises a problem that a sufficient amount of light cannot be guided to illuminate the body cavity. Therefore, the solid-state imaging device and the optical fiber bundle cannot be easily reduced in size or diameter.

  Therefore, there has been proposed a medical probe that can be made smaller in diameter than a conventional electronic scope (that is, an electronic scope equipped with a solid-state imaging device) by adopting a configuration that eliminates the need for the solid-state imaging device itself. Yes.

  An example of a medical observation system having this type of medical probe is disclosed in Patent Document 1. The medical probe described in Patent Literature 1 resonates the tip of a single optical fiber and scans an object with a predetermined scanning pattern with predetermined scanning light. Such a medical probe detects reflected light from an object, photoelectrically converts it, and sequentially outputs it to a video processor. The video processor processes the photoelectrically converted signal, images it, and outputs it to the monitor. The doctor can observe the image in the body cavity obtained in this way through a monitor in the same manner as when using an electronic scope, and can perform examinations and treatments.

US Pat. No. 6,563,105

  By the way, in the conventional electronic scope system, an abnormal image may appear in a part of the observation field according to the photographing situation. As a typical abnormal image, for example, there is an image caused by halation. The halation occurs according to the positional relationship between the tip of the electronic scope and the observation target, the scattering state of the reflected light from the observation target, and the like. The area in the observation field where halation has occurred becomes an image (so-called whiteout) in which the contrast is extremely lowered due to the saturation of the output of the light detector (so-called whiteout). Don't be. As a countermeasure when halation occurs, for example, a method of temporarily reducing the amount of illumination light is employed.

  Also in the medical observation system described in Patent Document 1, halation may appear in a part of the observation field for the same reason as the conventional electronic scope system. Also in this case, the occurrence of halation can be suppressed by temporarily reducing the amount of illumination light. However, the irradiation light used in this type of medical observation system is weak because it is irradiated onto the observation target via a single optical fiber. For this reason, when the amount of illumination light is reduced, the amount of light is further insufficient in the originally low luminance region of the observation field, and so-called black crushing occurs. That is, when the light source is dimmed to prevent the occurrence of halation, another problem arises that the image reproducibility of the dark area in the observation field is deteriorated. Deterioration of image reproducibility due to overexposure or blackout is undesirable because it is a factor that hinders accurate examination and treatment by a doctor.

  The present invention has been made in view of the above circumstances, and an object of the present invention is to provide a medical observation system suitable for processing abnormal images such as overexposure and blackout. is there.

  A medical observation system according to an aspect of the present invention that solves the above problem includes a light source that emits predetermined light, a scanning unit that scans light emitted from the light source on an object, and the scanning unit. Image signal detection means for receiving reflected light of the scanned light and detecting an image signal, and pixel arrangement of image information represented by each image signal based on detection timing of the image signal by the image signal detection means A pixel arrangement determining means for determining, an image creating means for creating an image by spatially arranging each image information according to the pixel arrangement determined by the pixel arrangement determining means, and an image detected at a timing corresponding to each pixel An intensity value detecting means for detecting the intensity value of the signal, and when the intensity value detected by the intensity value detecting means is a value not less than the first threshold value or not more than the second threshold value, a pixel corresponding to the intensity value is selected. Abnormal An abnormal pixel determining means for determining the element, a system which is characterized by having a defect pixel processing means for performing predetermined processing on a pixel-by-pixel basis against the abnormal pixel determined by the abnormal pixel determining means.

  According to the medical observation system of the present invention, since the determination regarding abnormal pixels is made finely on a pixel-by-pixel basis, appropriate countermeasures can be taken against abnormal images caused by various causes including overexposure and blackout. can do.

  For example, the abnormal pixel processing means diminishes or increases light at a timing when predetermined light is emitted toward a portion corresponding to the abnormal pixel in the object in order to correct an abnormality of the pixel in which whiteout or blackout occurs. The light source is configured to be driven and controlled. Since the amount of light emitted from the light source is controlled in units of pixels, for example, deterioration of image reproducibility due to whiteout can be satisfactorily eliminated, and deterioration of image reproducibility due to blackout can be effectively avoided.

  In addition, for example, the abnormal pixel processing unit is configured to recognize a pixel corresponding to the lesion as an abnormal pixel and highlight an image corresponding to the pixel. Since the lesioned part is discriminated on a pixel basis, the lesioned part can be highlighted with a fine contour that reproduces the precise shape.

  The medical observation system according to the present invention may further include a treatment light source that emits predetermined treatment light. In this case, the abnormal pixel processing means is configured to control the light emission of the treatment light source at a timing when the treatment light is irradiated to a portion corresponding to the abnormal pixel in the object. Since the range in which treatment light is irradiated is controlled in units of pixels, the burden on the living body during treatment is minimized.

  Here, when the intensity value detected by the intensity value detecting means is a value not less than the first predetermined value or not more than the second predetermined position with respect to the predetermined reference value, the abnormal pixel determining means It is good also as a structure which determines a corresponding pixel as an abnormal pixel. The abnormal pixel processing means, when light is radiated to a part corresponding to the abnormal pixel, reduces or increases the light intensity according to the difference value between the intensity value detected by the intensity value detection means and the reference value. It is good also as a structure to control.

  The medical observation system according to the present invention may further include an intensity value acquisition unit that initially acquires an intensity value corresponding to each pixel detected by the intensity value detection unit as a reference value of each pixel. In this case, the abnormal pixel determination unit determines for each pixel whether or not it is an abnormal pixel based on the reference value for each pixel acquired by the intensity value acquisition unit.

  Further, the medical observation system according to the present invention includes an intensity value acquisition unit that initially acquires an intensity value corresponding to each pixel detected by the intensity value detection unit, and each pixel acquired by the intensity value acquisition unit. Reference value calculating means for calculating an average value of intensity values as a reference value may be further included.

  Thus, according to the present invention, there is provided a medical observation system suitable for performing processing on abnormal images such as overexposure and blackout.

It is a schematic diagram which shows typically the internal structure of the scanning medical probe of 1st embodiment of this invention, and a one part structure of a processor. It is a block diagram which shows the structure of the processor and monitor of 1st embodiment of this invention. It is a sectional side view which shows the typical internal structure of the front-end | tip part of the scanning medical probe of 1st embodiment of this invention. It is an external appearance perspective view which shows the internal structure of the front-end | tip part of the scanning medical probe of 1st embodiment of invention. It is a figure for demonstrating the spot formed on an observation object. It is a figure which illustrates the analog signal detected by a photodetector when the observation object is irradiated with one pulse of combined pulse light in the first embodiment of the present invention. It is a block diagram which shows the structure of DSP which the processor of 1st embodiment of this invention has. It is a figure which shows notionally the data output from the peak value detection circuit which DSP of 1st embodiment of this invention has. It is a figure for demonstrating the specific example of the conversion process of the pixel address by the conversion circuit which DSP of 1st embodiment of this invention has. It is a block diagram which shows the structure of the abnormal pixel detection part which the processor of 1st embodiment of this invention has. It is a flowchart figure of the abnormal pixel process performed in the medical observation system of 1st embodiment of this invention. It is a schematic diagram which shows typically the internal structure of the scanning medical probe of 2nd embodiment of this invention, and a one part structure of a processor. It is a flowchart figure of the abnormal pixel process performed in the medical observation system of 2nd embodiment of this invention.

  Hereinafter, a medical observation system having a scanning medical probe according to an embodiment of the present invention will be described with reference to the drawings.

  FIG. 1 is a schematic diagram schematically showing an internal configuration of a scanning medical probe 100 and a partial configuration of a processor 200 according to the first embodiment of the present invention. FIG. 2 is a block diagram illustrating configurations of the processor 200 and the monitor 300 according to the first embodiment. In FIG. 2, in order to clarify the connection relationship between the scanning medical probe 100 and the processor 200, a part of the configuration of the scanning medical probe 100 is also schematically shown. Further, since the monitor 300 is an image receiving apparatus having a known configuration, the detailed configuration of the monitor 300 is not shown in FIG. As shown in these drawings, the medical observation system 1 of the first embodiment includes a scanning medical probe 100, a processor 200, and a monitor 300.

  The processor 200 controls the driving of the scanning medical probe 100 and generates an image signal based on the observation light acquired by the scanning medical probe 100, and the scanning medical medical device in a body cavity where natural light does not reach. The integrated processor includes a light source device that emits scanning light through the probe 100. In another embodiment, the signal processing device and the light source device may be configured separately.

  As shown in FIG. 2, the scanning medical probe 100 has an optical connector portion 110 and an electrical connector portion 120 at the proximal end portion. Further, the processor 200 includes an optical connector unit 210 and an electrical connector unit 220. By inserting the optical connector part 110 into the optical connector part 210, the scanning medical probe 100 and the processor 200 are optically connected. Similarly, when the electrical connector unit 120 is inserted into the electrical connector unit 220, the scanning medical probe 100 and the processor 200 are electrically connected. The processor 200 and the monitor 300 are electrically connected via a predetermined cable. In FIG. 1, in order to make it easy to understand the connection relationship between the scanning medical probe 100 and the processor 200, the connection portion between the optical connector portions 110 and 210 is divided into two.

  Thus, when the scanning medical probe 100, the processor 200, and the monitor 300 are connected to each other and the power is turned on, the operator can use the medical observation system 1 to examine and perform treatment in the body cavity of the patient. It becomes like this. Specifically, the operator inserts the insertion part 130 of the scanning medical probe 100 into the body cavity, guides the distal end 130a of the insertion part 130 to the vicinity of the observation target, and operates the operation part (not shown) of the processor 200. To do. The surgeon observes an image in the body cavity obtained as a result of such an operation through the monitor 300, and performs an examination, a treatment, or the like.

  In the first embodiment, the scanning medical probe 100 alone is directly inserted into the body cavity in order to observe the inside of the body cavity. In another embodiment, for example, in order to smoothly guide the distal end 130a to the vicinity of the observation target, the insertion portion 130 may be inserted with a guide wire or the like. In addition, for example, the insertion portion 130 may be inserted into a forceps channel of an electronic scope or the like to bring the distal end portion 130a close to the vicinity of the observation target.

Next, a series of processes until the image in the body cavity is displayed on the monitor 300 in the medical observation system 1 will be described in detail while explaining the configurations of the scanning medical probe 100 and the processor 200. Such a series of processing is
(1) Processing for acquiring observation light by scanning an observation target (2) Processing is broadly classified into processing for generating and displaying an image based on observation light.

First, “(1) processing for acquiring observation light by scanning an observation target” will be described. The processor 200 includes laser light sources 230R ₁ , 230R ₂ , 230G, and 230B that oscillate light corresponding to the wavelengths R ₁ , R ₂ , G, and B as light sources for scanning the observation target. Here, both R ₁ light and R ₂ light belong to the wavelength range of R light (including near-infrared light), but have different absorption rates depending on the state of hemoglobin. Specifically, R ₁ light is light in the vicinity of red and has a high absorption rate for reduced hemoglobin. R ₂ light is light in the vicinity of near-infrared light and has a high absorption rate for oxyhemoglobin. Thus, the reflection spectrum when the hemoglobin is simultaneously irradiated with light of both wavelengths R ₁ and R ₂ varies depending on the degree of oxidation of hemoglobin. Note that these four laser light sources have, for example, a single fiber laser that oscillates a broadband supercontinuum light or the like, and wavelength selective filters corresponding to the wavelengths R ₁ , R ₂ , G, and B. It may be replaced with a light source unit. Further, the light source is not limited to the laser light source, and may be a light source of another form such as an LED (Light Emitting Diode).

The processor 200 includes a system controller 240 that comprehensively controls signal processing timing and the like of each circuit of the processor 200. The system controller 240 outputs predetermined modulation control signals to the driver circuits of the drivers 232R ₁ , 232R ₂ , 232G and 232B. The drivers 232R ₁ , 232R ₂ , 232G and 232B directly modulate the laser light sources 230R ₁ , 230R ₂ , 230G and 230B based on the input modulation control signals, respectively. Specifically, each driver circuit passes currents having the same or different amplitudes to the corresponding laser light sources based on the modulation control signal. As a result, the laser light sources 230R ₁ , 230R ₂ , 230G, and 230B have the same or different intensity pulse light (hereinafter referred to as “R ₁ pulse light”) corresponding to the wavelengths R ₁ , R ₂ , G, and B, respectively. "R ₂ pulse light", "G pulse light", and "B pulse light") are oscillated at synchronized timing. The intensity of the pulsed light oscillated from each laser light source is a predetermined intensity except when irradiated to a part corresponding to an abnormal pixel described later. In the text, the predetermined intensity is defined as an intensity that changes as appropriate according to dimming control by a well-known dimming circuit (not shown).

R ₁ pulse light, R ₂ pulse light, G pulse light, and B pulse light oscillated from each laser light source are incident on the optical coupler 234. The optical coupler 234 combines and emits each incident pulsed light in a state where the phases are aligned. Hereinafter, for convenience of explanation, the pulsed light coupled by the optical coupler 234 is referred to as “coupled pulsed light”.

  When the light source is a light source unit composed of a single fiber laser and a wavelength selective filter, timing control for synchronizing the pulsed light of each wavelength is unnecessary. Therefore, there is an advantage that the circuit configuration around the laser light source can be simplified. Further, since the pulsed light that has already been coupled is oscillated, there is an advantage that the optical coupler 234 is unnecessary.

  The combined pulse light emitted from the optical coupler 234 is incident on the incident end 112 a of the single mode fiber 112 included in the scanning medical probe 100. The single mode fiber 112 is accommodated in an outer skin member (a sheath 132 shown in FIG. 3 described later) of the scanning medical probe 100 from the optical connector portion 110 to the distal end portion 130a. The coupled pulsed light incident on the incident end 112a is propagated by repeating total reflection inside the single mode fiber 112. The propagated coupled pulsed light is emitted from the emission end 112b of the single mode fiber 112 disposed inside the distal end portion 130a.

  In FIG. 3, the typical internal structure of the front-end | tip part 130a of 1st embodiment is shown with a sectional side view. FIG. 4 shows an external perspective view of the internal structure of the tip portion 130a of the first embodiment. In the following, in describing the configuration of the scanning medical probe 100, for convenience, the longitudinal direction of the scanning medical probe 100 is the Z direction, the two directions orthogonal to the Z direction and orthogonal to each other are the X direction, and Y Defined as direction. According to such a definition, for example, FIG. 3 is a cross-sectional view of the distal end portion 130 a in the YZ plane including the central axis AX of the scanning medical probe 100.

  The sheath 132 shown in FIG. 3 is a protective tube of the scanning medical probe 100 having flexibility. The sheath 132 has a shape extending from the distal end portion 130a to the optical connector portion 110, and protects various built-in components of the scanning medical probe 100. The outer diameter of the sheath 132 is much smaller than the outer diameter of a conventional electronic scope because the scanning medical probe 100 is configured not to mount a solid-state imaging device or the like. Therefore, the scanning medical probe 100 achieves even lower invasiveness than a conventional electronic scope.

  As shown in FIG. 3, a support 134 is supported inside the sheath 132. The tip 112c of the single mode fiber 112 is inserted into the through hole of the support 134 and is supported in a cantilever state. The support 134 also supports the actuators 136 and 138. The actuators 136 and 138 are piezoelectric actuators, and electrodes are formed at predetermined positions on the piezoelectric element. Each electrode has a terminal connected to an electric wire (not shown) housed in the electrical connector portion 120. Each electric wire is connected to the X-axis driver 236X or Y-axis driver 236Y of the processor 200 when the electric connector unit 120 and the electric connector unit 220 are connected.

  The system controller 240 outputs predetermined drive control signals to the driver circuits of the X-axis driver 236X and the Y-axis driver 236Y. The X-axis driver 236X applies a first AC voltage to the actuator 136 based on the drive control signal. The Y-axis driver 236Y applies a second AC voltage having the same frequency as the first AC voltage and having a phase orthogonal to the actuator 138 based on the drive control signal.

  The actuators 136 and 138 are configured by selecting materials and shapes so as to resonate in the X and Y directions when the first and second AC voltages are applied, respectively. The exit end 112b of the single mode fiber 112 is described as a surface that approximates the XY plane (hereinafter referred to as “XY approximate surface”) by combining the kinetic energy in the X and Y directions by the actuators 136 and 138. ) Draw a locus of a circle having a predetermined radius approximately centered on the central axis AX.

  The application of the AC voltage to the actuators 136 and 138 is stopped in a state where a circular locus having a predetermined radius is drawn. Then, the vibration of the tip 112c of the single mode fiber 112 is gradually attenuated. With such attenuation, the exit end 112b of the single mode fiber 112 moves toward the central axis AX while drawing a locus of a substantially spiral pattern on the XY approximate plane, and finally stops on the central axis AX. The coupled pulsed light is emitted during the period from immediately after the application of AC voltage to each actuator is stopped until the exit end 112b of the single mode fiber 112 is stopped on the central axis AX (hereinafter referred to as “spiral pattern period”). The injection continues from 112b.

  The distal end of the sheath 112 is sealed with a condenser lens 140. Therefore, the coupled pulse light is emitted from the exit end 112b of the single mode fiber 112 and once diverges, but is condensed by the condenser lens 140 to form a spot on the observation target. The spot diameter is extremely small, for example, on the order of several microns. A collimating lens (not shown) may be attached to the exit end 112b. In this case, the combined pulse light is emitted as parallel light from the emission end 112 b and forms a spot on the observation target via the condenser lens 140.

FIG. 5 is a diagram for explaining spots formed on the observation target. In order to obtain a single image, the scanning medical probe 100 draws n spots in the order of spots S ₁ , S ₂ , S ₃ ,..., S _n so as to draw a spiral pattern SP on the observation target. Form. The interval between the spots is determined depending on the movement speed of the exit end 112b of the single mode fiber 112, the modulation frequency of each laser light source, and the like. The spiral pattern SP is a virtual scanning locus drawn on the assumption that continuous light is scanned on the observation target instead of pulse light.

As a result of experiments and the like, the time taken to reach a state in which a locus of a circle having a predetermined radius is drawn after the exit end 112b of the single mode fiber 112 is stopped is known. Similarly, the time taken to start and end the spiral pattern period is also known. Further, the position of the exit end 112b of the single mode fiber 112 (or each spot formation position on the observation target) in the XY approximate plane during the spiral pattern period is also known. Therefore, based on such known information, the system controller 240 controls the timing for the X-axis driver 236X and the Y-axis driver 236Y (that is, the timing for applying and stopping the AC voltage to each actuator), and the drivers 232R ₁ , 232R ₂ , Timing control for 232G and 232B (that is, modulation control of each laser light source during the spiral pattern period) is repeated at a period corresponding to the frame rate.

  As shown in FIG. 4, a plurality of through holes arranged in an annular shape are formed on the end surface 134 a of the support 134. A detection fiber 142 is embedded in each through hole. Although not shown in FIG. 4, the detection fibers 142 are bundled behind the support 134 to form an optical fiber bundle 142B. The optical fiber bundle 142 </ b> B extends from the distal end portion 130 a to the optical connector portion 110, and the terminal end is accommodated in the optical connector portion 110.

  The end of the optical fiber bundle 142B is coupled to one end of the wavelength selection fiber 146 by an optical circulator 144. The fiber bundle 142B is merely a bundle of about several tens (for example, 80) optical fibers. Therefore, the fiber bundle 142B has a much smaller diameter than a conventional electronic scope or an optical fiber bundle of a fiberscope (for example, an optical fiber bundle in which several hundred to thousands of optical fibers are bundled). In the first embodiment, at least one detection fiber 142 is required. When the number of detection fibers 142 is one, the scanning medical probe 100 can be further reduced in diameter.

  Each spot of the combined pulse light formed on the observation target is reflected by the observation target and is incident on the inside of the sheath 132 via the condenser lens 140. The reflected pulsed light returned to the inside of the sheath 132 is incident on the incident end 142 a of each detection fiber 142. The reflected pulsed light incident on the incident end 142a is propagated toward the end in the fiber bundle 142B (detection fiber 142).

  The reflected pulse light propagated inside the fiber bundle 142B is incident on the coupling end of the wavelength selection fiber 146 coupled to the end of the fiber bundle 142B by the optical circulator 144. The optical circulator 144 is configured so that the reflected pulse light from the fiber bundle 142B is incident only on the wavelength selection fiber 146 (that is, the reflected pulse light from the fiber bundle 142B is not incident on the optical fiber 148 described later). .)

The wavelength selection fiber 146 is accommodated inside the optical connector unit 110 so as to wrap around. In the light guide path of the wavelength selection fiber 146, fiber Bragg gratings 146R ₁ , 146G, and 146B corresponding to the wavelengths R ₁ , G, and B are formed in order from the coupling end side. Accordingly, the reflected pulse light that is incident on the wavelength selection fiber 146 and propagated first causes strong back reflection of the R ₁ component by the fiber Bragg grating 146R ₁ . That is, the fiber Bragg grating 146R ₁ reflects only the R ₁ component pulse light (hereinafter referred to as “reflected R ₁ pulse light”) included in the reflected pulse light and returns it to the coupling end side of the wavelength selection fiber 146. At the same time, other components are permeated. The same optical action is also caused in the fiber Bragg grating 146G and the fiber Bragg grating 146B. That is, only the G light component (hereinafter referred to as “reflected G pulse light”) in the fiber Bragg grating 146G, and only the B light component (hereinafter referred to as “reflected B pulse light”) in the fiber Bragg grating 146B. Are reflected and returned to the coupling end side of the wavelength selection fiber 146.

The fiber Bragg gratings 146R ₁ , 146G, and 146B are formed with their positions determined so as to give a predetermined optical path difference to the reflected pulse light of each wavelength of R ₁ , G, and B. Here, the optical circulator 144 is configured so that the light from the wavelength selection fiber 146 is incident only on the optical fiber 148 (that is, the light from the wavelength selection fiber 146 is not incident on the fiber bundle 142B). Therefore, the reflected pulsed light of each wavelength that arrives at the coupling end of the wavelength selection fiber 146 with a predetermined time delay is sequentially incident on the optical fiber 148.

The end 148a of the optical fiber 148 is coupled to the photodetector 250 via a coupling lens 238 included in the processor 200 when the optical connector unit 110 and the optical connector unit 210 are connected. Accordingly, the reflected pulse light of each wavelength of the reflected R ₁ pulse light, reflected G pulse light, and reflected B pulse light is sequentially emitted from the terminal 148 a with a predetermined time delay and received by the photodetector 250.

The wavelength selection fiber 146 is bundled with the optical fiber 148 near the end. The terminal 146a of the wavelength selection fiber 146 is coupled to the photodetector 250 together with the terminal 148a when the optical connector unit 110 and the optical connector unit 210 are connected. The pulse light of the component corresponding to the R ₂ light included in the reflected pulse light from the fiber bundle 142B (hereinafter referred to as “reflected R ₂ pulse light”) is propagated through the wavelength selection fiber 146 in any fiber Bragg grating. The light is emitted from the end 146 a of the wavelength selection fiber 146 without being reflected by the light and is received by the photodetector 250.

In the scanning medical probe 100, the light guide path length in the wavelength selection fiber 146 from the coupling end to the optical fiber bundle 142B to the fiber Bragg grating 146B is defined as L1, and from the coupling end to the wavelength selection fiber 146 to the end 148a. When the light guide path length in the optical fiber 148 is defined as L2, and the light guide path length in the wavelength selection fiber 146 from the fiber Bragg grating 146B to the end 146a is defined as L3,
L3> L1 + L2
It is configured to satisfy. Therefore, the reflected R ₂ pulsed light is emitted from the end 146a after being given a longer time delay than the reflected B pulsed light. Therefore, the reflected pulse light of each wavelength is received by the photodetector 250 with a predetermined time delay in the order of reflected R ₁ pulse light, reflected G pulse light, reflected B pulse light, and reflected R ₂ pulse light.

  As described above, the combined pulse light is guided by the single single mode fiber 112 and irradiates the observation target. Therefore, the amount of reflected pulsed light reflected from the observation target is very small. In order to detect such weak light reliably and with low noise, the photodetector 250 employs a highly sensitive photodetector such as a photomultiplier tube.

  The above is the description of “(1) processing for acquiring observation light by scanning an observation target”. Next, “(2) processing for generating and displaying an image based on observation light”, that is, processing for imaging the acquired observation light (reflection pulse light of each wavelength) and displaying it on the monitor 300 will be described.

The photodetector 250 photoelectrically converts the received reflected pulse light of each wavelength to generate an analog signal and outputs it to a subsequent circuit. FIG. 6 shows an example of an analog signal detected by the photodetector 250 when the observation target is irradiated with one pulse of combined pulse light in the first embodiment. The vertical axis in FIG. 6 represents the output voltage value (unit: V), and the horizontal axis represents time (unit: sec). Referring to FIG. 6, the waveform λ ₂ of the reflected G pulse light has a delay of t ₂ -t ₁ (sec) with respect to the waveform λ ₁ of the reflected R ₁ pulse light, and the waveform λ ₃ of the reflected B pulse light has the reflected G The delay of t ₃ -t ₂ (sec) with respect to the waveform λ ₂ of the pulsed light, and the waveform λ ₄ of the reflected R ₂ pulsed light is t ₄ -t ₃ (sec) with respect to the waveform λ ₃ of the reflected B pulsed light. It can be seen that each delay is given.

  By the way, in each fiber Bragg grating, for example, in consideration of the time resolution of the photodetector 250, the waveform of the reflected pulsed light of each wavelength is surely separated (that is, the output waveform of FIG. ) Are formed so as to be separated so as to be surely formed). However, as the fiber Bragg gratings are separated from each other, the time delay amount of the reflected pulse light of each wavelength increases, and the specifications (high resolution, high frame rate, etc.) that require a high-speed clock cannot be satisfied. The harmful effects of Accordingly, each fiber Bragg grating is formed with an appropriate interval in consideration of all these matters. Each value of the light guide path lengths L1 to L3 is set in consideration of the resolution of the image, the frame rate, the time resolution of the photodetector 250, and the like, as in each fiber Bragg grating.

  For example, consider a case where the half width of the waveform of the reflected pulsed light of each wavelength is 10 nsec. In this case, in order to make valleys appear between the waveforms of the reflected pulsed light of each wavelength, it is considered appropriate that the interval between the fiber Bragg gratings is, for example, about 1 m.

  An analog signal corresponding to the reflected pulse light of each wavelength detected by the photodetector 250 is sampled and held, and converted into a digital signal sequence by the A / D converter 252. The converted digital signal sequence is input to a DSP (Digital Signal Processor) 254.

  FIG. 7 is a block diagram showing the configuration of the DSP 254 of the first embodiment. As shown in FIG. 7, the DSP 254 includes a waveform accumulation memory 254a, a peak value detection circuit 254b, a conversion circuit 254c, a peak value accumulation memory 254d, and a peak value readout circuit 254e.

  The waveform storage memory 254a latches the digital signal sequence from the A / D converter 252. The latched digital signal sequence is sequentially discarded after a predetermined time has elapsed in consideration of the capacity of the waveform storage memory 254a.

Peak value detecting circuit 254b is inflection point monitors the digital signal sequence which is latched in the waveform storage memory 254a, i.e. the peak value P ₁ of the waveform lambda ₁ as shown in the peak value (e.g. FIG. _6, the waveform lambda ₂ peaks the value _{P 2,} the waveform lambda ₃ of the peak value _{P 3,} the peak value _{P 4} of the waveform lambda ₄₎ for detecting a. Then, when the peak value in the digital signal sequence is detected, that is, the time (e.g., time t ₁ corresponding to the peak value P ₁ shown in FIG. _6, the time t ₂ corresponding to the peak value P _2, the peak value P ₃ in time _{t 3} corresponding, time _{t 4)} corresponding to the peak value _{P 4} sequentially outputs the conversion circuit 254c in association with the peak value.

FIG. 8 is a conceptual diagram of data output from the peak value detection circuit 254b. As shown in FIG. 8, the peak value detecting circuit 254b, the data associated with the peak value P and time T corresponding to the spot _S 1 to S _n (hereinafter, referred to as "association data".) The conversion circuit 254c Are output sequentially.

  The conversion circuit 254c converts the time T of the association data into, for example, a pixel address referred to as a solid-state image sensor. Specifically, the conversion circuit 254c holds a conversion table of time T and pixel address corresponding to each spot in advance. Such a conversion table is created based on the formation position and formation time of each spot during the spiral pattern period, which is known information. When the association data corresponding to the specific time T is input, the conversion circuit 254c converts the specific time T into a specific pixel address based on the conversion table.

A specific example of pixel address conversion processing by the conversion circuit 254c will be described with reference to FIG. Here, for convenience of explanation, a case is considered in which each time T of association data is converted into a 19 × 19 pixel address. For example, when the association data of the times t ₁₁ , t ₂₁ , t ₃₁ , and t ₄₁ corresponding to the spot S ₁ is input, the conversion circuit 254c, based on the conversion table, sets the times t ₁₁ , t ₂₁ , t ₃₁ , and t _41. Is converted into a pixel address (3, 10). Next, when the association data of the times t ₁₂ , t ₂₂ , t ₃₂ , and t ₄₂ is input, the time times t ₁₂ , t ₂₂ , t ₃₂ , and t ₄₂ are set to the pixel address (3, 8) based on the conversion table. Convert. The conversion circuit 254c sequentially performs the conversion process to the pixel address on the input association data.

By the conversion processing to the pixel address, for example, four output voltage values, that is, peak values P ₁₁ , P ₂₁ , P ₃₁ , and P ₄₁ are associated with the pixel address (3, 10). However, it is not clear which color information the peak values P ₁₁ , P ₂₁ , P ₃₁ , and P ₄₁ have only by this. Therefore, the conversion circuit 254c gives appropriate color information to the four peak values. For this purpose, the conversion circuit 254c uses the delay time of the peak value of each wavelength that is predetermined based on the distance between the fiber Bragg gratings corresponding to each wavelength and the length relationships of the light guide path lengths L1 to L3.

That is, the conversion circuit 254c adds the color information indicating that the peak value _{P 11} detected to the time _{t 11} corresponding to the spot _{S 1} is _{R 1} color. Then, the color information indicating the color G from time _{t 11} to the predetermined time (Fig. 6, _t 2 _-t 1 (sec)) delayed time _{t 21} the peak value _{P 21} detected in, from the time _{t 11} Color information indicating the B color is added to the peak value P ₃₁ detected at a time t ₃₁ delayed by a predetermined time (t ₃ -t ₁ (sec) in FIG. 6). Further, near infrared light (referred to as “R ₂ color” for convenience) is detected in the peak value P ₄₁ detected at time t ₄₁ delayed by a predetermined time (t ₄ -t ₁ (sec) in FIG. 6) from time t ₁₁ . Color information indicating that is added.

In this way, the conversion circuit 254c allows the R ₁ color, G color, B color, and R ₂ color luminance values associated with the pixel address (3, 10) (in other words, the intensity of the signal of each color). Image information whose values are peak values P ₁₁ , P ₂₁ , P ₃₁ , P ₄₁ is generated. The conversion circuit 254c sequentially performs such color information addition processing on the input association data.

The conversion circuit 254c sequentially outputs and writes the generated image information to the peak value storage memory 254d. For pixel addresses that do not have image information, for example, predetermined masking data is generated and output to the peak value storage memory 254d for writing. Peak value storage memory 254d is a frame buffer, buffering the image information of one frame corresponding to the generated spots S ₁ to S _n by the conversion circuit 254c. The peak value reading circuit 254e reads the image information buffered in the peak value storage memory 254d according to the timing control by the system controller 240, and outputs it to the video signal output circuit 256.

The video signal output circuit 256 converts the input image information into NTSC (National Television).
The video signal is converted into a video signal conforming to a predetermined standard such as Standards Committee or PAL (Phase Alternating Line), and output to the monitor 300. On the monitor 300, a color image to be observed consisting of R ₁ color, G color, and B color is displayed. The R _two- color image is selectively added to the color image according to the setting by the user operation. When the image of the R _2-color is set to be added to the color image, the video signal output circuit 256 performs for example other colors image and a predetermined highlighting display processing on the image of the R ₂ colors to allow distinction.

  Here, as described above, the image observed through the scanning medical probe 100 is caused by whiteout caused by the occurrence of halation or black crushing caused by dimming of illumination light for suppressing halation. Image reproducibility may deteriorate. Therefore, the medical observation system 1 has a configuration described below so as not to cause black crushing while quickly eliminating whiteout caused by the occurrence of halation.

Specifically, the processor 200 includes an abnormal pixel detection unit 258 connected to the DSP 254. FIG. 10 is a block diagram illustrating a configuration of the abnormal pixel detection unit 258. As illustrated in FIG. 10, the abnormal pixel detection unit 258 includes an LUT (Look up Table) 258a, comparators 258R ₁ , 258R ₂ , 258G, 258B, abnormal pixel storage units 258R ₁ ′, 258R ₂ ′, 258G ′, 258B ′. FIG. 11 is a flowchart of abnormal pixel processing executed by the abnormal pixel detection unit 258 in cooperation with other components of the processor 200. The abnormal pixel processing is continuously executed, for example, from when the medical observation system 1 is started to when it is stopped. In the following description and drawings in the text, the processing step is abbreviated as “S”.

The peak value storage memory 254d of the DSP 254 outputs image information for one frame that is buffered first after the medical observation system 1 is activated to the LUT 258a. As shown in FIG. 11, the LUT 258a associates the pixel address with the luminance value of each wavelength (R ₁ , R ₂ , G, B) based on the input from the peak value storage memory 254d, as shown in FIG. A similar table is initially generated and held (S1). The luminance value of each wavelength in each pixel held in the LUT 258a is used in the subsequent processing steps as the reference luminance value of each wavelength in each pixel when a normal part is imaged. The table initially held in the LUT 258a is deleted, for example, when the medical observation system 1 is stopped. The subsequent processing steps (S2 to S8) are respectively performed on the image information of each wavelength of each pixel. The processing of S2 to S8 for the image information of all the wavelengths of all the pixels is repeatedly executed in one frame cycle.

  The table generated by the process of S1 may be stored in advance in the LUT 258a. In this case, the reference luminance value is, for example, a value obtained from experience. By preparing the reference luminance value in advance, the execution of the process of S1 is omitted. In order to improve the accuracy of the reference luminance value, for example, a calculation circuit (not shown) on the DSP 254 side calculates the average luminance value of each wavelength in each pixel using image information for a plurality of frames, and calculates each calculated luminance value. The average luminance value may be output and held in the LUT 258a as a reference luminance value for each wavelength in each pixel.

Incidentally, it is not necessary to set the reference luminance value for each pixel or for each wavelength as described above. For example, the calculation circuit on the DSP 254 side may calculate the average value of the luminance values of all the pixels, and output the calculated average luminance value to the LUT 258a as a reference luminance value that is commonly used by all the pixels, and hold it. . Common to all the pixels of the reference luminance _{value, R 1, R 2, G} , may be separately calculated luminance values for each wavelength of _B, or R _1, R _{2, G,} the luminance values of all wavelengths B It is good also as a luminance value common to all the wavelengths calculated based on it. The LUT 258a only needs to store the reference luminance value, and does not need to store a table in which the pixel address and the reference luminance value are associated with each other. Therefore, the LUT 258a can be configured with an inexpensive small-capacity memory having a high access speed corresponding to, for example, a high resolution and a high frame rate.

The peak value storage memory 254d outputs image information for the second and subsequent frames to a comparator corresponding to each wavelength. Specifically, the peak value storage memory 254d, the predetermined order of the luminance values of _{R 1} to the comparator 258R ₁ of each pixel (e.g., spots _{S 1, S 2, S 3} , ···, corresponding to _{S n} Output in the order of Similarly, the peak value storage memory 254d outputs the luminance values of R ₂ , G, and B of each pixel to the comparators 258R ₂ , 258G, and 258B in a predetermined order. In the following, the luminance value input to each comparator is referred to as “actually measured luminance value” to distinguish it from the reference luminance value.

LUT258a outputs in the same order as the reference luminance value of each wavelength at each pixel in the comparators (i.e., spots _{S 1, S 2, S 3} , ···, order corresponding to _{S n).} Specifically, LUT258a outputs the reference luminance value of the _{R 1} of each pixel to the comparator 258R ₁ in a predetermined order. Similarly, the LUT 258a outputs the reference luminance values of the R ₂ , G, and B wavelengths of each pixel to the respective comparators 258R ₂ , 258G, and 258B in a predetermined order. The system controller 240 controls the output timing of each luminance value so that the actually measured luminance value and the reference luminance value at the same pixel address are input to each comparator at a synchronized timing.

The comparators 258R ₁ , 258R ₂ , 258G, 258B compare the measured luminance value input at the synchronized timing with the reference luminance value, respectively, and use the difference value as an abnormal pixel storage unit 258R ₁ ′, 258R ₂ ′, The data is output to 258G ′ and 258B ′ (S2). Each comparator outputs a positive difference value when the measured luminance value is higher than the reference luminance value, and outputs a negative difference value when the measured luminance value is lower than the reference luminance value.

  Each abnormal pixel storage unit determines whether or not the pixel is an abnormal pixel based on the difference value corresponding to each pixel (S3). Specifically, each abnormal pixel storage unit, when the difference value between the actually measured luminance value and the reference luminance value is equal to or greater than a (a> 0) (S3: YES), the light detector 250 of the pixel concerned. Since the output is saturated or just before saturation (that is, whiteout or substantially whiteout due to halation or the like), the address of the pixel is stored as an abnormal pixel with extremely high luminance (S4). ). Hereinafter, for the convenience of explanation, “abnormal pixel with extremely high luminance” is referred to as “high luminance abnormal pixel”.

  The system controller 240 has a conversion table similar to the conversion circuit 254c, in which each pixel address is associated with the emission timing of the pulsed light corresponding to the pixel. In the process of S5, the system controller 240 converts the address of the high-brightness abnormal pixel stored in each abnormal pixel storage unit into the emission timing of the pulsed light of each laser light source based on the conversion table. Next, the system controller 240 generates a modulation control signal for performing dimming control of the pulsed light at the converted light emission timing, and outputs the modulation control signal to each driver circuit. Each laser light source oscillates pulsed light with a lower intensity than the predetermined intensity at the timing corresponding to the high-intensity abnormal pixel by modulation control by the driver circuit based on the modulation control signal, and determines it at other timing (that is, the high-intensity abnormal pixel) At a timing corresponding to a pixel that has not been performed, pulsed light having a predetermined intensity is oscillated. Note that the light reduction amount of the pulsed light may be set according to a difference value between the actually measured luminance value and the reference luminance value. The abnormal pixel process of FIG. 11 returns to the process of S2 after executing the process of S5.

  The part corresponding to the whiteout or substantially whiteout region is irradiated with the attenuated pulsed light. Therefore, whiteout or substantial whiteout caused by halation or the like is quickly eliminated, and image reproducibility is improved. Since the pulsed light is not dimmed at the part corresponding to the region other than the high luminance abnormal pixel, the adverse effect of black crushing due to insufficient light quantity can be effectively avoided. That is, according to the medical observation system 1, since the light amount control of the pulsed light is controlled in units of pixels, the deterioration of the image reproducibility due to whiteout is satisfactorily eliminated, and the deterioration of the image reproducibility due to blackout is reduced. Effectively avoided.

  The medical observation system 1 further has a function of assisting accurate examination and treatment by a doctor by capturing pixels in the region corresponding to the lesioned part in the observation visual field as abnormal pixels. Hereinafter, for convenience of explanation, “a pixel in an area corresponding to a lesion” is referred to as “lesion abnormal pixel”.

  Specifically, in the process of S6, each abnormal pixel storage unit determines that the measured luminance value of the pixel is significantly lower than the reference luminance value, and the difference value is a value equal to or less than b (b <0) (S3: NO, S6: YES), the pixel address is stored as a lesion abnormal pixel (S7). For example, when a plurality of abnormal lesion pixels stored in the abnormal pixel storage unit form a spatially continuous pixel arrangement, the video signal output circuit 256 performs a cooperative process with the system controller 240 to correspond to the lesion part corresponding to the pixel arrangement. The region is subjected to outline emphasis etc. and displayed on the monitor 300 (S8). The abnormal pixel process of FIG. 11 returns to the process of S2 after executing the process of S8. For pixels whose difference value between the measured luminance value and the reference luminance value is smaller than a and larger than b (S3: NO, S6: NO), the pulsed light dimming process in S5 or the emphasis in S8. None of the display processing is executed. That is, according to the medical observation system 1, the lesioned part is determined on a pixel-by-pixel basis, so that the lesioned part can be highlighted with a fine outline that reproduces a fine shape.

For example, consider a case where the hemoglobin oxygen saturation level of a living body is examined using the medical observation system 1. Since the R ₁ light is absorbed as the reduced hemoglobin concentration in the living body increases, the number of pixels in which the actually measured luminance value of R ₁ becomes lower than the reference luminance value increases. As a result, the distribution of reduced hemoglobin is highlighted over a relatively wide range on the monitor 300. On the other hand, the higher the oxyhemoglobin concentration in the living body, the more the R ₂ light is absorbed, and therefore the number of pixels whose measured luminance value of R ₂ becomes lower than the reference luminance value increases. As a result, the distribution of oxyhemoglobin is highlighted on the monitor 300 over a relatively wide range. A doctor can observe the distribution of reduced hemoglobin or oxygenated hemoglobin to examine the hemoglobin oxygen saturation of the living body.

The processing of S6 to S8 does not need to be performed for all wavelengths R ₁ , R ₂ , G, and B, and may be performed only for the wavelengths necessary to achieve the inspection purpose and the like. For example, if you want to inspect the hemoglobin oxygen saturation, only with respect to the wavelength of R _2, or process only S6~S8 respect two wavelengths of R ₁ and R ₂ may be executed.

By the way, there is an individual difference in the absorption rate of R ₁ light or R ₂ light according to the degree of oxidation of hemoglobin. To test the hemoglobin oxygen saturation of the living body more accurate, by replacing the value b to be referred to in the processing of S6 example the difference value c of the luminance values of R ₁ and the luminance values of R _2, abnormal pixel in FIG. 11 Processing may be executed. In this case, a process for calculating the difference value c of each pixel is added as a pre-process of S6.

According to the medical observation system 1 of the first embodiment, a lesion part having a high absorption rate for at least one wavelength among R ₁ , R ₂ , G, and B is detected, and a lesion part by a doctor is detected. Inspection becomes possible. When inspecting other lesions by performing special light observation such as fluorescence observation, the wavelength of the pulsed light irradiated to the observation target may be appropriately selected according to the inspection purpose.

In the first embodiment, a high luminance abnormal pixel or a lesion abnormal pixel is determined in accordance with the level of the actually measured luminance value based on the reference luminance value. In another embodiment, in order to simplify the respective components of the processor 200 that executes the abnormal pixel processing of FIG. 11, pixels having a luminance value equal to or higher than the first fixed value in the processing of S3 and S4 are set as high luminance abnormal pixels. In the processes of S6 and S7, a pixel having a luminance value equal to or lower than the second fixed value may be determined uniformly as a lesion abnormal pixel. The first and second fixed values may be set for the wavelengths R ₁ , R ₂ , G, and B, respectively, or may be set in common for all wavelengths.

  FIG. 12 is a schematic diagram similar to FIG. 1 schematically showing an internal configuration of the scanning medical probe 100z and a partial configuration of the processor 200z according to the second embodiment of the present invention. FIG. 13 is a flowchart of abnormal pixel processing executed in the medical observation system 1z of the second embodiment. In the second embodiment, the same or similar components as those of the first embodiment are denoted by the same or similar reference numerals, and description thereof is omitted.

  In the medical observation system 1z, image generation and lesion detection are performed using pulsed light of three wavelengths of R, G, and B. The processor 200z includes a treatment laser light source 230s that oscillates treatment laser light suitable for treatment of a lesion, in addition to a laser light source that oscillates pulsed light of R, G, and B wavelengths. As shown in FIG. 13, in the second embodiment, the processes of S1 to S7 are executed as in the first embodiment, and the process of S9 is executed instead of the process of S8. However, in the modification of the second embodiment, the processes of S8 and S9 may be executed together.

  In the process of S9, as in the process of S5, the system controller 240 refers to a conversion table that associates each pixel address with the emission timing of the pulsed light corresponding to the pixel. Based on the referred conversion table, the system controller 240 converts the address of the abnormal lesion pixel stored in each abnormal pixel storage unit into the emission timing of the therapeutic laser beam by the therapeutic laser light source 230s. Next, the system controller 240 generates a modulation control signal for controlling the light emission of the therapeutic laser light at the converted light emission timing, and outputs it to a driver circuit (not shown) for the therapeutic laser light source 230s. The therapeutic laser light source 230s oscillates a therapeutic laser beam at a timing corresponding to a lesion abnormal pixel and irradiates the lesioned part by modulation control by a driver circuit based on the modulation control signal. That is, according to the medical observation system 1, since the range irradiated with the therapeutic laser beam is controlled in units of pixels, the burden on the living body at the time of treatment can be minimized. The therapeutic laser beam may be either continuous light or pulsed light.

  The above is the description of the embodiment of the present invention. The present invention is not limited to the above-described configuration, and various modifications can be made within the scope of the technical idea of the present invention. For example, in another embodiment of the medical observation system, an optical separator that separates the used wavelengths is coupled to the proximal end of the fiber bundle 142B, and the reflected pulse light of each wavelength separated by the optical separator is a separate photodetector. It is good also as a structure detected by this. In this case, optical parts such as the optical circulator 144, the wavelength selection fiber 146, and the optical fiber 148 are reduced.

  In the medical observation system according to another embodiment, the following process may be executed as an alternative to the process of S3 to S5 or in combination with the process of S3 to S5. That is, each abnormal pixel storage unit, for example, when a measured luminance value of a pixel is significantly lower than a reference luminance value and the difference value is a value equal to or less than d (d <0), The address of the pixel is stored as Next, the system controller 240 converts the address of the low-luminance abnormal pixel stored in each abnormal pixel storage unit into the light emission timing of the pulsed light of each laser light source based on the same conversion table as in the process of S5. The system controller 240 generates a modulation control signal for controlling the increase of pulsed light at the converted light emission timing, and outputs the modulation control signal to each driver circuit. Each laser light source oscillates pulsed light with a higher intensity than the predetermined intensity at the timing corresponding to the low-luminance abnormal pixel by modulation control by the driver circuit based on the modulation control signal, and determines that it is at other timing (that is, low-luminance abnormal pixel) At a timing corresponding to a pixel that has not been performed, pulsed light having a predetermined intensity is oscillated. Thereby, for example, a portion that has been crushed black due to insufficient light quantity is irradiated with light stronger than other portions. For this reason, black crushing and the like are quickly eliminated. Note that the light increase amount of the pulsed light may be set according to a difference value between the actually measured luminance value and the reference luminance value.

  The photodetector 250 is not limited to the configuration of the processor 200 or 200z. In another embodiment, the scanning medical probe 100 or 100z may include a photodetector 250.

  Further, the scanning medical probe 100 or 100z has a wavelength selection filter such as a dielectric multilayer filter instead of the fiber Bragg grating as a means for giving a light path difference to each wavelength of light and causing a time delay. It is good also as a structure.

1 Medical Observation System 100 Scanning Medical Probe 200 Processor 240 System Controller 254 DSP
258 Abnormal Pixel Detection Unit 300 Monitor

Claims (8)

A light source that emits predetermined light;
Scanning means for scanning the emitted light on the object;
Image signal detecting means for detecting an image signal by receiving reflected light of the scanned light;
Pixel arrangement determining means for determining a pixel arrangement of image information represented by each image signal based on the detection timing of the image signal;
Image creating means for spatially arranging the image information according to the determined pixel arrangement to create an image;
An intensity value detecting means for detecting an intensity value of an image signal detected at a timing corresponding to each of the pixels;
When the detected intensity value is a value equal to or greater than a first threshold value or equal to or less than a second threshold value, an abnormal pixel determination unit that determines a pixel corresponding to the intensity value as an abnormal pixel;
Abnormal pixel processing means for performing predetermined processing in units of pixels on the determined abnormal pixels;
A medical observation system characterized by comprising:   The abnormal pixel processing means drives and controls the light source so that the light is dimmed or increased at a timing when the light is emitted toward a portion corresponding to the abnormal pixel in the object. Item 2. The medical observation system according to Item 1.   The medical observation system according to claim 1, wherein the abnormal pixel processing unit highlights an image corresponding to the abnormal pixel. A treatment light source that emits predetermined treatment light;
The said abnormal pixel processing means carries out light emission control of the said light source for treatment at the timing with which the said treatment light is irradiated to the site | part corresponding to the said abnormal pixel in the said object, The Claim 1 to Claim 3 characterized by the above-mentioned. The medical observation system according to any one of the above.   The abnormal pixel determining means responds to the intensity value when the intensity value detected by the intensity value detecting means is a value not less than a first predetermined value or not more than a second predetermined position with respect to a predetermined reference value. The medical observation system according to any one of claims 1 to 4, wherein a pixel to be determined is determined as an abnormal pixel.   The abnormal pixel processing unit controls a light reduction amount or a light increase amount of light emitted from the light source according to a difference value between the intensity value detected by the intensity value detection unit and the reference value. The medical observation system according to claim 5, which refers to claim 2. Intensity value acquisition means for initially acquiring the intensity value corresponding to each of the pixels detected by the intensity value detection means as the reference value of each pixel;
The said abnormal pixel determination means determines whether it is an abnormal pixel for every said pixel based on the acquired reference value for every pixel, either of Claim 5 or Claim 6 characterized by the above-mentioned. The medical observation system according to one item. Intensity value acquisition means for initially acquiring an intensity value corresponding to each of the pixels detected by the intensity value detection means;
A reference value calculation means for calculating an average value of the acquired intensity values for each pixel as the reference value;
The medical observation system according to claim 5, further comprising:

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