JP2008289560A - Fluorescence endoscope apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To acquire a spectral decomposition image at a high frame rate. <P>SOLUTION: The fluorescence endoscope apparatus 1 includes: a light source unit 3 for generating excitation light to the observation part of a living body to which a fluorescent probe is injected beforehand; a variable spectroscopic element 29 for selecting the return light of a prescribed wavelength range from return light returning from the living body; a CCD 31 for detecting the return light of the wavelength range selected by the variable spectroscopic element 29; an image processing part 43 for decomposing the spectrum of the fluorescent probe on the basis of the return light detected by the CCD 31; an input part 33 for inputting the kind of the fluorescent probe and an observation method; a memory 35 for making the control method of the light source unit 3, the variable spectroscopic element 29 and the image processing part 43 correspond to the kind of the fluorescent probe and the observation method and storing them; and a control part 37 for reading the wavelength range and setting corresponding to the kind of the fluorescent probe and the observation method of the control method input by the input part 33 from the memory 35 and controlling the light source unit 3, the variable spectroscopic element 29 and the image processing part 43. <P>COPYRIGHT: (C)2009,JPO&INPIT

Description

  The present invention relates to a fluorescence endoscope apparatus.

In endoscopic observation, observing a fluorescent image is useful for diagnosing and observing a lesion because information on a living body different from a reflected image can be obtained. For example, if a fluorescent probe that emits fluorescence by binding to a substance derived from a lesion is administered, the concentration distribution of the substance derived from the lesion can be observed by observing the fluorescence image. In addition, by observing autofluorescence, that is, fluorescence from a fluorescent substance that naturally exists in the living body, it is possible to observe changes in the living body and observe the state of the lesion.
However, when the fluorescence wavelength range of the fluorescent probe is the same as the wavelength range of the autofluorescence, it is not possible to distinguish between the fluorescence of the fluorescence probe and the autofluorescence if the fluorescence is acquired using a bandpass filter. Can not make an accurate diagnosis.

In response to this problem, in recent years, when observing a sample containing a plurality of fluorescent probes with a microscope, the spectrum data of the fluorescence of the sample is acquired using a liquid crystal tunable filter that can select the acquisition wavelength, and the spectrum is obtained. There has been proposed a technique for calculating the type of fluorescent probe present at each point of a sample and its existence ratio using a deconvolution method or the like (see Patent Document 1).
US Pat. No. 6,403,947

  However, in endoscopy, it is desirable to obtain a high frame rate because the object to be observed moves under the influence of pulsation. When the technique disclosed in Patent Document 1 is used in endoscopy If the number of wavelengths to be acquired is large, the object to be observed moves during the generation of the multiband image, so that there is a problem that an accurate spectrum cannot be acquired.

  The present invention has been made in view of such circumstances, and an object thereof is to provide a fluorescence endoscope apparatus that acquires a spectrally separated image at a high frame rate.

In order to solve the above problems, the present invention employs the following means.
The present invention relates to an illumination light source that generates excitation light for exciting the fluorescent labeling substance or an autofluorescent substance that is naturally present in the living body with respect to an observation part of the living body into which the fluorescent labeling substance has been previously injected, and the illumination light source Of the return light returning from the living body by irradiating the excitation light from a wavelength selection means for selecting the return light in a predetermined wavelength range, and detecting the return light in the wavelength range selected by the wavelength selection means A detection means; a spectrum separation means for separating the spectrum of the fluorescent labeling substance based on the return light detected by the detection means; an input means for inputting the type and observation method of the fluorescent labeling substance; and the fluorescence Corresponding to the type of the labeling substance and the observation method, the wavelength range of the excitation light emitted from the illuminating means, the characteristics of the return light selected by the wavelength selecting means A storage means for storing a wavelength range showing an appropriate wavelength characteristic and the setting of the spectrum separating means; and the wavelength range and the setting corresponding to the type and the observation method of the fluorescent labeling substance inputted by the input means, Provided is a fluorescence endoscope apparatus including a control unit that reads out from a storage unit and controls the illumination unit, the wavelength selection unit, and the spectrum separation unit.

  According to the present invention, the excitation light generated from the illumination light source is irradiated on the observation part of the living body into which the fluorescent labeling substance has been injected in advance, and the wavelength selection means operates, so that the predetermined wavelength range in the return light returning from the living body Return light is selected. The return light selected by the wavelength selection means is detected by the operation of the detection means. Then, the spectrum of the fluorescent labeling substance is separated based on the return light detected by the detection means by the operation of the spectrum separation means.

  In this case, when the type of the fluorescent labeling substance and the observation method are input by the operation of the input means, the type of the fluorescent labeling substance and the observation method are stored in the storage means by the operation of the control means. The illumination light source, wavelength selection means, and spectrum separation means are controlled in accordance with the wavelength range and setting.

That is, excitation light in a wavelength range suitable for the type of fluorescent labeling substance and the observation method is irradiated on the observation unit, and return light in the wavelength range showing characteristic wavelength characteristics is selected by the wavelength selection means. Thereby, the minimum necessary information for extracting the spectrum of the return light can be acquired, and based on the acquired information, the spectrum of the fluorescent labeling substance can be obtained by the spectrum separating means.
Therefore, it is not necessary to separate the spectrum by detecting the return light over the entire wavelength range, and it is possible to shorten the time for acquiring the spectrum separated image and improve the frame rate.

In the above invention, the characteristic wavelength characteristic may be a wavelength characteristic including a peak intensity.
With this configuration, it is possible to efficiently limit the observation range to a location where the concentration of the fluorescent labeling substance or the autofluorescent substance is high.

In the above invention, the observation method input by the input means may be fluorescence observation or reflected light observation.
With this configuration, when a lesion is present in the observation unit, information regarding the lesion can be obtained by observing the fluorescence.

  For example, by observing the fluorescence of the fluorescent labeling substance, the concentration distribution of the substance derived from the lesion can be observed, and information relating to the shape and size of the lesion can be obtained. In addition, by observing the fluorescence of the autofluorescent substance, changes in the living body can be observed, and information regarding the state of the lesion can be obtained. On the other hand, by observing the reflected light, it is possible to observe the density of blood vessels, the state of accumulation, and the like, and for example, information on lesions such as inflammation can be acquired.

Moreover, in the said invention, it is good also as providing the elongate insertion part inserted in a body cavity, and the said detection means being arrange | positioned at the front-end | tip of this insertion part.
With such a configuration, the detecting means for detecting the return light incident on the elongated insertion portion is arranged at the distal end of the insertion portion, so that the insertion portion inserted into the body cavity can be made compact.

Further, in the above-mentioned invention, it is provided with an elongated insertion portion to be inserted into a body cavity, and a light guide means for guiding the return light along the longitudinal direction of the insertion portion, and on the proximal end side of the insertion portion, The detection means may be arranged.
The detection unit is arranged on the proximal end side of the elongated insertion part inserted into the body cavity, and the return light incident on the insertion part is guided to the detection unit by the operation of the light guide unit, so that the distal end side of the insertion unit is slimmed Operability can be improved.

Further, in the above invention, the wavelength selecting means is formed with a coat layer on the opposing surfaces of two optical substrates arranged to face each other with a gap therebetween, and the etalon type variable spectroscopic element capable of changing the gap It is good also as being.
With such a configuration, it is possible to arbitrarily adjust the interval between the two optical substrates and transmit the return light having a desired wavelength according to the interval.

  According to the present invention, there is an effect that a spectrum separation image can be acquired at a high frame rate by observing a fluorescent probe, observing autofluorescence, and observing reflected light in a narrow band.

Hereinafter, a fluorescence endoscope apparatus according to an embodiment of the present invention will be described with reference to the drawings.
The fluorescence endoscope apparatus 1 according to the present embodiment is an electronic scope type endoscope as shown in FIG. The fluorescence endoscope apparatus 1 includes a light source device (illumination light source) 3 that generates excitation light that irradiates a living body observation unit, an endoscope 5 that performs observation inside a body cavity, and the light source device 3 and the endoscope 5. And a control device 7 for controlling.

  The light source device 3 is attached to a xenon lamp 9 that emits light including a visible broadband from the infrared wavelength band, and a filter turret 11, and selectively selects light in a predetermined wavelength band from the light emitted from the xenon lamp 9. And a pump 15 that rotates the filter turret 11 to switch the plurality of excitation filters 13, and an excitation light control circuit 17 that controls driving of the motor 15.

  The filter turret 11 is formed in a substantially disc shape and has a rotation axis parallel to the optical axis of the xenon lamp 9. A plurality of excitation filters 13 are concentrically attached to the filter turret 11 at equal distances from the rotation axis. As the excitation filter 13, for example, a filter that transmits excitation light in a wavelength band of 420 nm, 530 nm, 400 nm to 440 nm, 630 nm to 670 nm, 680 nm to 740 nm, 700 nm to 770 nm, or the like is attached.

  The motor 15 sequentially arranges the excitation filters 13 on the optical axis of the xenon lamp 9 by rotating the filter turret 11 around the rotation axis. Thereby, the excitation light of a predetermined wavelength band emitted from the xenon lamp 9 and transmitted through the excitation filter 13 arranged on the optical axis is emitted from the light source device 3.

  The endoscope 5 includes an elongated insertion portion 19 that is inserted into a body cavity, and includes a light guide fiber 21 that guides excitation light emitted from the light source device 3 to the distal end of the insertion portion 19. At the distal end of the insertion portion 19, an illumination lens 23 that emits excitation light guided by the light guide fiber 21 into the body cavity, and return light that returns from the body cavity by the excitation light emitted through the illumination lens 23. And an imaging unit 25 for observing the image.

  The imaging unit 25 includes an objective lens 27 that condenses the return light from inside the body cavity, and a variable spectroscopic element (wavelength selection means) that transmits the return light in a predetermined wavelength band among the return light collected by the objective lens 27. ) 29, and a CCD (detection means) 31 that captures the return light transmitted through the variable spectroscopic element 29 and generates an electrical signal corresponding to the fluorescence luminance for each of the two-dimensionally arranged pixels.

  The variable spectroscopic element 29 is an etalon-type optical filter in which an optical coat layer is formed on opposing surfaces of two optical substrates (not shown) arranged to face each other with a parallel interval, and the interval can be changed. is there. The variable spectroscopic element 29 includes a sensor electrode (not shown) of a capacitance sensor that detects the center wavelength of the transmittance characteristics of these two optical substrates, and an actuator (not shown) that changes the distance. ing.

  The variable spectroscopic element 29 transmits only light having a wavelength determined according to the center wavelength of the transmittance characteristic, and reflects the remaining light. For example, as shown in FIG. 2, the transmittance characteristic of the variable spectroscopic element 29 can transmit light in a wavelength band having a full width at half maximum of 10 nm with respect to the center wavelength 520 (nm). By changing the center wavelength of the transmittance characteristics of the two optical substrates, the center wavelength of the transmittance characteristics can be moved to transmit light in a desired wavelength band. The light transmitted through the variable spectroscopic element 29 is incident on the CCD 31, converted into an electric signal, and output to the control device 7.

  The control device 7 corresponds to an input unit (input means) 33 for inputting the type of fluorescent probe (fluorescent labeling substance) to be administered to a living body and an observation method, and the type of fluorescent probe input to the input unit 33 and the observation method. In addition, the light source device 3, the variable spectroscopic element 29, and a memory (storage unit) 35 for storing a control method of an image processing unit (spectral separation unit) 43 described later, and the control method stored in the memory 35, the light source device. 3. a control unit (control means) 37 that controls the variable spectral element 29 and the image processing unit 43; a variable spectral element control circuit 39 that receives a drive signal from the control unit 37 and drives the actuator of the variable spectral element 29; An image generation circuit 41 that receives an image acquisition signal from the control unit 37 to drive the CCD 31 and receives an electrical signal from the CCD 31 to generate image information; and an image generation circuit 41 And an image processing unit 43 for processing the image information et input.

The input unit 33 includes, for example, a fluorescein compound such as FITC (in this embodiment, “fluorescein fluorescence” is adopted), a rhodamine compound such as Rhodamine B, indocyanine green, Cydye (GE Healthcare Biosciences). (In this embodiment, “Cy5.5 fluorescence” and “Cy7 fluorescence” are employed.), Bodipy compounds such as Bodipy-FL, porphyrin compounds or precursors of porphyrin compounds , Alexa
A fluorescent probe such as Fluor Dye (manufactured by Molecular Probes) is selected and input. Moreover, the presence or absence of observation of autofluorescence is input. Note that a plurality of fluorescent probes and autofluorescence can be selected in combination.

  The input unit 33 is configured to select and input fluorescence observation or reflected light observation as an observation method. In the present embodiment, when the fluorescent probe is input, fluorescence observation is indirectly selected as an observation method, and when NBI (narrow band reflected light) is input, it is indirectly selected as an observation method. In the following description, it is assumed that the reflected light observation is selected. The input unit 33 is configured to output the input fluorescent probe type and observation method to the control unit 37.

  In the memory 35, the wavelength range of the excitation light emitted from the light source device 3 in correspondence with the type of the fluorescent probe and the observation method, the wavelength range indicating the characteristic wavelength characteristic of the return light selected by the variable spectroscopic element 29, and image processing A control method related to the presence or absence of spectrum separation by the unit 43 is stored. For example, the following control methods of combination examples 1 to 5 are stored.

(Combination example 1: NBI (narrow band reflected light) is observed)
(1) The wavelength of the excitation filter 13 is 420 nm, the center wavelength of the transmittance characteristic of the variable spectral element 29 is 420 nm, and there is no spectral separation.
(2) The wavelength of the excitation filter 13 is 530 nm, the center wavelength of the transmittance characteristic of the variable spectral element 29 is 530 nm, and there is no spectral separation.

(Combination example 2: When observing autofluorescence + fluorescein fluorescence)
(1) The wavelength 400 nm to 440 nm of the excitation filter 13 and the wavelength range 500 nm to 550 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectrum separation.
(2) The wavelength between 400 nm to 440 nm of the excitation filter 13 and 600 nm to 630 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectrum separation.

(Combination example 3: When observing Cy5.5 fluorescence + Cy7 fluorescence)
(1) The wavelength of 630 nm to 670 nm of the excitation filter 13 and the wavelength range of 690 nm to 730 nm of the variable spectroscopic element 29 are acquired every 10 nm, with spectral separation.
(2) The wavelength of 680 nm to 740 nm of the excitation filter 13 and the range of 760 nm to 840 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectral separation.

(Combination example 4: When observing Cy7 fluorescence + indocyanine green fluorescence)
(1) The wavelength of 680 nm to 740 nm of the excitation filter 13 and the range of 760 nm to 850 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectral separation.
(2) The wavelength of 700 nm to 770 nm of the excitation filter 13 and the range of 810 nm to 840 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectrum separation.

(Combination example 5: When observing autofluorescence + fluorescein fluorescence + indocyanine green fluorescence)
(Autofluorescence + fluorescein fluorescence)
(1) The wavelength 400 nm to 440 nm of the excitation filter 13 and the wavelength range 500 nm to 550 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectrum separation.
(2) The wavelength between 400 nm to 440 nm of the excitation filter 13 and 600 nm to 630 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectrum separation.
(Indocyanine green fluorescence)
(3) Wavelengths of 700 nm to 770 nm of the excitation filter 13 and 810 nm to 850 nm of the variable spectroscopic element 29 are acquired every 10 nm, and there is spectral separation.

  The control unit 37 receives an input signal from the input unit 33 and reads a control method corresponding to the input signal from the memory 35. The control unit 37 is configured to output a selection signal for the excitation filter 13 to the excitation light control circuit 17 of the light source device 3 based on the read control method. The control unit 37 outputs an actuator drive signal to the variable spectroscopic element control circuit 39, outputs an image acquisition signal of the CCD 31 to the image generation circuit 41, and outputs a spectrum separation signal to the image processing unit 43. ing.

The image generation circuit 41 outputs image information generated based on the electrical signal from the CCD 31 to the image processing unit 43.
The image processing unit 43 receives the spectrum separation signal from the control unit 37 and performs spectrum separation on the image information input from the image generation circuit 41. A known spectral deconvolution method is used for the spectral separation.

  The procedure of the known spectral deconvolution method is to obtain the emission spectrum of the fluorescent probe in advance or use the catalog value of the emission spectrum of the fluorescent probe to register the emission spectrum of each fluorescent probe in the computer and The spectrum is measured, and the emission spectrum of the measurement object is decomposed into the spectrum of the fluorescent probe using deconvolution to determine the existence ratio of each fluorescent probe.

For example, a case where three types of fluorescent probes are used will be described. The three types of fluorescent probes have known fluorescence spectra. The spectrum of fluorescent probe 1 is Fl1 (λ), the spectrum of fluorescence 2 is Fl2 (λ), and the spectrum of fluorescent probe 3 is Fl3 (λ). The spectrum S (λ) in a state where three types of fluorescent probes are mixed is
(Formula 1)
S (λ) = A1 × Fl1 (λ) + A2 × Fl2 (λ) + A3 × Fl3 (λ)
Given in. Here, A1, A2, and A3 are coefficients based on the abundance of the fluorescent probe.

  In the present embodiment, by changing the center wavelength of the transmittance characteristic using the etalon-type variable spectroscopic element 29, images in a wavelength band having a full width at half maximum of 10 nm are obtained at a plurality of points. Spectral data S (λ) corresponding to the pixel is acquired. When fluorescence images are acquired at three or more points, in (Equation 1), since Fli (λ) is known spectral data, the coefficients A1 to A3 are used by using, for example, the known Inverse Least Square method. By solving, the ratio of each fluorescent probe can be determined.

  The image processing unit 43 is connected to a monitor 45 provided outside the control device 7. The image processing unit 43 causes the monitor 45 to display image information that has undergone spectrum separation by the spectrum deconvolution method.

The operation of the fluorescence endoscope apparatus 1 according to this embodiment configured as described above will be described with reference to FIG.
In order to observe the observation part of the living body with the fluorescence endoscope apparatus 1 according to the present embodiment, first, the insertion part 19 of the endoscope 5 is inserted into the body of the living body into which the fluorescent probe has been injected in advance, and the control device 7. The type and observation method of the fluorescent probe are input to the input unit 33. (Step S1). Hereinafter, the combination example 2 described above (when observing autofluorescence + fluorescein fluorescence) will be described as an example.

  When “autofluorescence” and “fluorescein fluorescence” are input to the input unit 33, the control unit 37 reads from the memory 35 a control method corresponding to “autofluorescence” and “fluorescein fluorescence” input to the input unit 33. Read. Then, a selection signal for the excitation filter 13 is output from the control unit 37 to the excitation light control circuit 17, and the excitation filter 13 that transmits only light having a wavelength of 400 nm to 440 nm is disposed on the optical axis (step S2). As a result, excitation light having a wavelength band of 400 nm to 440 nm is emitted from the light source device 3 and is irradiated onto the living body observation unit via the illumination lens 23 of the insertion unit 19.

  Further, the control unit 37 outputs a drive signal for moving the range of the transmittance characteristics of the variable spectroscopic element 29 in the range of 500 nm to 550 nm and 600 nm to 630 nm every 10 nm to the variable spectroscopic element control circuit 39. In the variable spectroscopic element 29, the actuator is operated in response to the drive signal from the variable spectroscopic element control circuit 39, and first, two sheets are arranged so that the center wavelength of the transmittance characteristic of the variable spectroscopic element 29 becomes the initial position of 500 nm. The optical substrate is moved (step S3).

  Subsequently, an image acquisition signal of the CCD 31 is output from the control unit 37 to the image generation circuit 41. In the CCD 31, the light transmitted through the variable spectroscopic element 29 is photographed, and image acquisition of the living body observation unit is started. As a result, the center wavelength of the transmittance characteristic of the variable spectroscopic element 29 changes from 500 nm to 550 nm and 600 nm to 630 nm, and images in a wavelength band with a full width at half maximum of 10 nm are sequentially acquired (step S4).

  Thereby, for example, as shown in FIG. 4, fluorescein fluorescence A, autofluorescence B of normal tissue, and autofluorescence C of a tumor part exhibiting characteristic wavelength characteristics in a wavelength band of 500 nm to 550 nm and a wavelength band of 600 nm to 630 nm. Is obtained. In the figure, the vertical axis represents fluorescence intensity (arbitrary unit), and the horizontal axis represents wavelength (nm).

  The image acquired by the CCD 31 is converted into an electrical signal and output to the image generation circuit 41, and image information is generated in the image generation circuit 41. In the control unit 37, it is determined whether or not all fluorescent images in the designated wavelength band have been acquired (step S5). If it is determined that all the fluorescence images in the designated wavelength band have not been acquired (step S5 “NO”), the process returns to step S3, and the operations in steps S3 to S5 are repeated.

  On the other hand, when the control unit 37 determines that all the fluorescence images in the designated wavelength band have been acquired (step S5 “YES”), a spectrum separation signal is output from the control unit 37 to the image processing unit 43. . In the image processing unit 43, image information is input from the image generation circuit 41, and spectrum separation is performed by the spectrum deconvolution method (step S6).

In this embodiment, when the spectrum of fluorescein fluorescence A is A1 × Fl1 (λ) and the spectrum of autofluorescence B is A2 × Fl2 (λ),
(Formula 2)
S (λ) = A1 × Fl1 (λ) + A2 × Fl2 (λ)
Thus, the abundance ratio of the fluorescent probe (fluorescein fluorescence A) can be determined.

  In the control unit 37, it is determined whether or not all observations of the control method have been completed (step S7). If it is determined that all the observations have not been completed (step S7 “NO”), the process returns to step S2, and the operations of steps S2 to S7 are repeated. On the other hand, if it is determined that all the observations have been completed (step S7 “YES”), the fluorescein fluorescence A and the autofluorescence B are pseudo-colored in different colors in the image processing unit 43, and after spectral separation. Image information is displayed on the monitor 45 (step S8).

  In this case, as shown in FIG. 4, for example, fluorescein fluorescence A and normal tissue autofluorescence B each have a wavelength characteristic that peaks in the wavelength band of 500 nm to 550 nm. When the image information is displayed on the monitor 45, as shown in FIG. 5A, it is difficult to distinguish between the fluorescein fluorescence A part (reference numeral 47 in the figure) and the autofluorescence B part (reference numeral 49 in the figure).

  On the other hand, by displaying the image information after the spectrum separation on the monitor 45, as shown in FIG. 5B, for example, the fluorescein fluorescence A emitted from the cancer tissue (see reference numeral 47 in the figure) is emitted. Can stand out. This makes it possible to obtain a clear spectrum separation image.

  As described above, according to the fluorescence endoscope apparatus 1 according to the present embodiment, the observation unit is irradiated with excitation light in a wavelength range suitable for the type of the fluorescent probe and the observation method, and exhibits characteristic wavelength characteristics. Since we decided to observe the return light in the wavelength range, obtain the minimum information necessary to extract the spectrum of the return light, and efficiently limit the observation range to locations with high concentrations of fluorescent probes and autofluorescence. can do. This eliminates the need to detect the return light over the entire wavelength range and separate the spectrum, thereby shortening the time for obtaining the spectrally separated image and improving the frame rate.

In addition, by adopting the etalon type variable spectroscopic element 29, it is possible to arbitrarily adjust the distance between the two optical substrates and transmit the desired return light according to the center wavelength of the transmittance characteristic. In addition, information regarding the shape and size of a lesion and information regarding a lesion such as a change in a living body can be obtained by fluorescence observation.
In this embodiment, the fluorescence observation is described as an example. However, when the reflected light observation is performed, the density of blood vessels, the state of accumulation, and the like can be observed. For example, information on lesions such as inflammation Can be obtained.

Moreover, the fluorescence endoscope apparatus 1 according to the present embodiment can be modified as follows.
For example, the fluorescence endoscope apparatus 1 according to the present embodiment has been described by exemplifying the electronic scope type endoscope 5, but instead of this, as shown in FIG. 6, a fiber scope type endoscope 51 may be adopted. In this case, the camera head 57 including the imaging lens 55, the variable spectroscopic element 29, and the CCD 31 is disposed on the proximal end side of the insertion portion 53, and the objective lens 27 is provided at the distal end of the insertion portion 53. An image guide fiber (light guide means) 59 that guides the return light incident through the camera head 57 to the camera head 57 and an eyepiece lens 57 may be incorporated in the insertion portion 53.
By providing the variable spectroscopic element 29 and the CCD 31 on the proximal end side of the insertion portion 53, the insertion portion 53 can be slimmed. Thereby, the operativity of the endoscope 51 can be improved.

  In addition, for example, as a fluorescent probe, an antibody or peptide labeled with the fluorescent probe exemplified in this embodiment may be used. For example, Her2 receptor antibody often found in breast cancer, somatostatin (ligand for somatostatin receptor) labeled with Cy5.5 fluorescence, CEA (Carcinoembryonic Antigen) antibody used as a marker for adenocarcinoma, fluorescein Those combined with fluorescence may be used.

  Further, for example, when displaying autofluorescence image information on the monitor 45, different colors may be assigned to the fluorescence in the wavelength band of 500 nm to 550 nm and the fluorescence in the wavelength band of 600 nm to 630 nm. Moreover, it is good also as assigning and displaying one color to the result of having performed the division of (fluorescence of the wavelength band of 600 nm-630 nm) / (fluorescence of the wavelength band of 500 nm-550 nm).

  Further, for example, in the present embodiment, the variable spectroscopic element 29 has been exemplified and described as the wavelength selection unit, but a liquid crystal tunable filter may be employed instead.

1 is a schematic configuration diagram of a fluorescence endoscope apparatus according to an embodiment of the present invention. It is the figure which showed the relationship between the wavelength range and transmittance | permeability of the variable spectral element of FIG. It is a flowchart figure which shows operation | movement of the fluorescence endoscope apparatus of FIG. It is a spectrum figure of the return light obtained by the fluorescence endoscope apparatus of FIG. FIG. 5A is a diagram showing a monitor display before spectrum separation, and FIG. 5B is a diagram showing a monitor display after spectrum separation. It is a schematic block diagram of the fluorescence endoscope apparatus which concerns on the modification of one Embodiment of this invention.

Explanation of symbols

1 Fluorescence endoscope device 3 Light source device (illumination light source)
29 Variable spectral element (wavelength selection means)
31 CCD (detection means)
33 Input section (input means)
35 Memory (storage unit)
37 Control part (control means)
43 Image processing section

Claims (6)

An illumination light source that generates excitation light for exciting the fluorescent labeling substance or the autofluorescent substance that is naturally present in the living body with respect to the observation part of the living body into which the fluorescent labeling substance has been previously injected;
Wavelength selecting means for selecting return light in a predetermined wavelength range among return light returning from the living body by irradiating the excitation light from the illumination light source;
Detecting means for detecting the return light in the wavelength range selected by the wavelength selecting means;
Spectrum separating means for separating the spectrum of the fluorescent labeling substance based on the return light detected by the detecting means;
Input means for inputting the type and observation method of the fluorescent labeling substance;
Corresponding to the type of the fluorescent labeling substance and the observation method, the wavelength range of the excitation light emitted from the illumination unit, the wavelength range indicating the characteristic wavelength characteristic of the return light selected by the wavelength selection unit, and Storage means for storing settings of the spectrum separating means;
The wavelength range and the setting corresponding to the type and the observation method of the fluorescent labeling substance input by the input unit are read from the storage unit, and the illumination unit, the wavelength selection unit, and the spectrum separation unit are controlled. And a fluorescent endoscope device.   The fluorescence endoscope apparatus according to claim 1, wherein the characteristic wavelength characteristic is a wavelength characteristic including a peak intensity.   The fluorescence endoscope apparatus according to claim 1, wherein the observation method input by the input unit is fluorescence observation or reflected light observation. An elongated insertion portion to be inserted into the body cavity,
The fluorescence endoscope apparatus according to any one of claims 1 to 3, wherein the detection means is disposed at a distal end of the insertion portion. An elongated insertion portion to be inserted into the body cavity;
Light guide means for guiding the return light along the longitudinal direction of the insertion portion,
The fluorescence endoscope apparatus according to any one of claims 1 to 3, wherein the detection unit is disposed on a proximal end side of the insertion portion.   2. The etalon-type variable spectroscopic element according to claim 1, wherein the wavelength selecting unit is an etalon-type variable spectroscopic element that is formed by forming a coat layer on the opposing surfaces of two optical substrates that are arranged to face each other with a gap therebetween. Item 6. The fluorescent endoscope device according to any one of Items 5 to 6.

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