U.S. patent application number 12/169161 was filed with the patent office on 2008-11-13 for endoscope device.
This patent application is currently assigned to OLYMPUS CORPORATION. Invention is credited to Kazuhiro Gono, Tetsuo Nonami.
Application Number | 20080281154 12/169161 |
Document ID | / |
Family ID | 27481475 |
Filed Date | 2008-11-13 |
United States Patent
Application |
20080281154 |
Kind Code |
A1 |
Gono; Kazuhiro ; et
al. |
November 13, 2008 |
ENDOSCOPE DEVICE
Abstract
An endoscope device obtains tissue information of a desired
depth near the tissue surface. A xenon lamp (11) in a light source
(4) emits illumination light. A diaphragm (13) controls a quantity
of the light that reaches a rotating filter. The rotating filter
has an outer sector with a first filter set, and an inner sector
with a second filter set. The first filter set outputs frame
sequence light having overlapping spectral properties suitable for
color reproduction, while the second filter set outputs narrow-band
frame sequence light having discrete spectral properties enabling
extraction of desired deep tissue information. A condenser lens
(16) collects the frame sequence light coming through the rotating
filter onto the incident face of a light guide (15). The diaphragm
controls the amount of the light reaching the filter depending on
which filter set is selected.
Inventors: |
Gono; Kazuhiro; (Kanagawa,
JP) ; Nonami; Tetsuo; (Tokyo, JP) |
Correspondence
Address: |
SCULLY SCOTT MURPHY & PRESSER, PC
400 GARDEN CITY PLAZA, SUITE 300
GARDEN CITY
NY
11530
US
|
Assignee: |
OLYMPUS CORPORATION
Tokyo
JP
|
Family ID: |
27481475 |
Appl. No.: |
12/169161 |
Filed: |
July 8, 2008 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10333155 |
Jan 16, 2003 |
|
|
|
12169161 |
|
|
|
|
Current U.S.
Class: |
600/109 |
Current CPC
Class: |
A61B 1/043 20130101;
A61B 5/0071 20130101; A61B 1/063 20130101; A61B 1/0638 20130101;
A61B 1/0646 20130101; A61B 5/0084 20130101; A61B 1/0669
20130101 |
Class at
Publication: |
600/109 |
International
Class: |
A61B 1/05 20060101
A61B001/05 |
Foreign Application Data
Date |
Code |
Application Number |
Jul 21, 2000 |
JP |
2000-221312 |
Jul 27, 2000 |
JP |
2000-227237 |
Jul 27, 2000 |
JP |
2000-227238 |
Mar 26, 2001 |
JP |
2001-088256 |
Claims
1. An endoscope device, comprising: an illumination light supplying
section for supplying illumination light including a visible light
region; an endoscope having image-pickup section for irradiating
the illumination light on a subject and picking up an image of the
subject by return light; a signal processing section for signal
processing image-pickup signals from the image-pickup section; and
a band restricting section for restricting to narrow a band of at
least one of a plurality of wavelength regions of the illumination
light and performing image formation of a band image of a discrete
spectral distribution of the subject on the image-pickup section,
the band restricting section being disposed to be arrangeable on an
optical path from the illumination light supplying section to the
image-pickup section, wherein the signal processing section
performs spatial frequency filtering processing for each of
wavelength regions of the image-pickup signals with the band of the
at least one wavelength region narrowed by the band restricting
section.
2. The endoscope device according to claim 1, wherein the
illumination light supplying unit comprises a light quantity
control unit for controlling the quantity of light of the
illumination light for each of the wavelength regions, according to
restriction by the band restricting unit.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] The present application is a continuation application of (1)
U.S. application Ser. No. 10/333,155 filed on Jan. 16, 2003, which
claims priority based on (2) Japanese Patent Application No.
2000-221312 applied in Japan on Jul. 21, 2000, (3) Japanese Patent
Application No. 2000-227237 applied in Japan on Jul. 27, 2000, (4)
Japanese Patent Application No. 2000-227238 applied in Japan on
Jul. 27, 2000, and (5) Japanese Patent Application No. 2001-88256
applied in Japan on Mar. 26, 2001 claiming priority based on the
aforementioned Japanese Patent Application No. 2000-221312 applied
in Japan on Jul. 21, 2000, and the contents disclosed in the
aforementioned (1) through (5) have been referenced to in the
present specification, Claims, and drawings and are incorporated
herein by reference.
TECHNICAL FIELD
[0002] The present invention relates to an endoscope device which
captures images of living body tissue and performs signal
processing thereon.
BACKGROUND ART
[0003] Conventionally, endoscope devices for irradiating
illumination light and obtaining endoscopic images within body
cavities have been widely used. With such endoscope devices, an
electronic endoscope has image-pickup means for introducing an
illumination light from a light source device into the body cavity
using a light guide or the like and captures an image of the
subject with the return light, and image-pickup signals from the
image-pickup means are subjected to signal processing with a video
processor, thereby displaying an endoscopic image on an observation
monitor, so that an observation portion such as an affected area or
the like is observed.
[0004] In the event of performing normal living body tissue
observation with an endoscope device, white light of the visible
light region is emitted with a light source device, frame sequence
light is irradiated on the subject via, for example, a rotating
filter such as RGB or the like, and the return light from this
frame sequence light is synchronized with a video processor, so as
to obtain a color image, or a color chip is disposed at the front
face of the image-pickup surface of the image-pickup means of the
endoscope and an image is captured by dividing the return light
from white light into RGB, and image processing is performed at the
video processor, thereby obtaining a color image.
[0005] On the other hand, the absorption properties and scattering
properties of the light at the living body tissue differ according
to the wavelength of the irradiated light, so in recent years,
various types of infrared light endoscope devices, which are
capable of observing the tissues at the deep part of the living
body tissue by irradiating infrared light on the living body tissue
as the illumination light, for example, are proposed.
[0006] However, with living body tissue diagnosis, while the deep
tissue information near the surface of the tissue is also an
important object of observation, with the above-described infrared
light endoscope devices, only the deep tissue information deeper
than the tissue surface can be obtained.
[0007] Also, in the event of irradiating white light on the living
body tissue as RGB frame sequential light from a rotating filter,
the wavelength regions thereof differ, so while image-pickup
signals from light of each color has different deep part tissue
information near the tissue surface of the living body tissue, but
generally, the white light is separated into an RGB light with each
of the wavelength regions overlapping, in order to obtain a more
natural color image for the endoscopic image by the RGB frame
sequential light.
[0008] That is, with overlapped RGB light, there is a problem that
desired deep tissue information near the surface of the tissue of
the living body tissue cannot be readily recognized, since a broad
range of the deep tissue information is taken into the image-pickup
signals of the light of each wavelength region.
[0009] The present invention has been made in the light of the
above-described situation, and first, it is an object thereof to
provide an endoscope device and light source device capable of
obtaining tissue information of a desired depth near the tissue
surface of the living body tissue.
[0010] Also, it is a second object of the present invention to
provide an endoscope device whereby tissue information of a desired
depth near the tissue surface of the living body tissue can be
separated and visually recognized.
DISCLOSURE OF INVENTION
[0011] The endoscope device according to the present invention
comprises illumination light supplying means for supplying
illumination light including visible light region; an endoscope
having image-pickup means for irradiating the illumination light on
a subject and capturing an image of the subject by return light;
and signal processing means for signal processing of image-pickup
signals from the image-pickup means; wherein band restricting
means, for restricting at least one of the plurality of wavelength
regions of the illumination light and performing image formation of
a band image of a discrete spectral distribution of the subject on
the image-pickup means, are provided on the optical path from the
illumination light supplying means to the image-pickup means.
BRIEF DESCRIPTION OF THE DRAWINGS
[0012] FIG. 1 is a configuration diagram illustrating the
configuration of an endoscope device according to a first
embodiment of the present invention.
[0013] FIG. 2 is a configuration diagram illustrating the
configuration of a rotating filter shown in FIG. 1.
[0014] FIG. 3 is a diagram illustrating the spectral properties of
a first filter set of the rotating filter shown in FIG. 2.
[0015] FIG. 4 is a diagram illustrating the spectral properties of
a second filter set of the rotating filter shown in FIG. 2.
[0016] FIG. 5 is a diagram illustrating the structure of the living
body tissue in the layer direction to be observed with the
endoscope device shown in FIG. 1.
[0017] FIG. 6 is a diagram describing the state of the illumination
light from the endoscope device shown in FIG. 1 reaching the living
body tissue in the layer direction.
[0018] FIGS. 7a-c are diagrams illustrating each of the band images
from frame sequence light transmitted through the first filter set
shown in FIG. 3.
[0019] FIGS. 8a-c are diagrams illustrating each of the band images
from frame sequence light transmitted through the second filter set
shown in FIG. 4.
[0020] FIG. 9 is a diagram describing light adjustment control
performed by a light adjusting circuit shown in FIG. 1.
[0021] FIG. 10 is a diagram illustrating the spectral properties of
a first modification made on the second filter set of the rotating
filter shown in FIG. 2.
[0022] FIG. 11 is a diagram illustrating the spectral properties of
a second modification made on the second filter set of the rotating
filter shown in FIG. 2.
[0023] FIG. 12 is a diagram illustrating the spectral properties of
a third modification made on the second filter set of the rotating
filter shown in FIG. 2.
[0024] FIG. 13 is a diagram illustrating the spectral properties of
a fourth modification made on the second filter set of the rotating
filter shown in FIG. 2.
[0025] FIG. 14 is a diagram illustrating a first example of
spectral distribution of a xenon lamp shown in FIG. 1.
[0026] FIG. 15 is a diagram illustrating the spectral properties of
a fourth modification made on the second filter set of the rotating
filter in the event that the spectral distribution of the xenon
lamp shown in FIG. 14 is applied.
[0027] FIG. 16 is a diagram illustrating spectral properties of
living body tissue illumination light with the fourth modification
made on the second filter set of the rotating filter shown in FIG.
2.
[0028] FIG. 17 is a diagram illustrating a second example of
spectral distribution of the xenon lamp shown in FIG. 1.
[0029] FIG. 18 is a diagram illustrating an example of spectral
sensitivity properties of the CCD shown in FIG. 1.
[0030] FIG. 19 is a diagram illustrating the spectral properties of
a light reduction filter to be applied by vapor deposition to a
fifth modification made on the second filter set of the rotating
filter in the event that the spectral distribution of the xenon
lamp is that in the second example and the spectral sensitivity
properties of the CCD are those shown in FIG. 18.
[0031] FIG. 20 is a diagram illustrating the spectral properties of
the fifth modification made on the second filter set to which the
light reduction filter shown in FIG. 19 has been applied by vapor
deposition.
[0032] FIG. 21 is a configuration diagram illustrating a first
modification of the light source device shown in FIG. 1.
[0033] FIG. 22 is a configuration diagram illustrating the
configuration of the light reduction rotating filter shown in FIG.
21.
[0034] FIG. 23 is a configuration diagram illustrating the
configuration of a second modification made on the light source
device shown in FIG. 1.
[0035] FIG. 24 is a diagram illustrating the light reduction
properties of a first light reduction filter making up the light
reduction filter shown in FIG. 23.
[0036] FIG. 25 is a diagram illustrating the light reduction
properties of a second light reduction filter making up the light
reduction filter shown in FIG. 23.
[0037] FIG. 26 is a diagram illustrating the light reduction
properties of the light reduction filter shown in FIG. 23.
[0038] FIG. 27 is a diagram illustrating an example illustrating
detailed spectral properties of the second filter set of the
rotating filter shown in FIG. 2.
[0039] FIG. 28 is a diagram illustrating the spectral properties of
a sixth modification made on the second filter set of the rotating
filter shown in FIG. 2.
[0040] FIG. 29 is a diagram illustrating the configuration of the
principal components of a modification made on the video processor
shown in FIG. 1.
[0041] FIG. 30 is a first diagram describing the operation of the
video processor shown in FIG. 29.
[0042] FIG. 31 is a second diagram describing the operation of the
video processor shown in FIG. 29.
[0043] FIG. 32 is a diagram illustrating the spectral properties of
a seventh modification made on the second filter set of the
rotating filter shown in FIG. 2.
[0044] FIG. 33 is a diagram illustrating the spectral properties of
the seventh modification made on the second filter set shown in
FIG. 32.
[0045] FIG. 34 is a configuration diagram illustrating the
configuration of an endoscope device according to a second
embodiment of the present invention.
[0046] FIG. 35 is a configuration diagram illustrating the
configuration of the rotating filter shown in FIG. 34.
[0047] FIG. 36 is a diagram illustrating the spectral properties of
the color chip shown in FIG. 34.
[0048] FIG. 37 is a configuration diagram illustrating the
configuration of an endoscope device according to a third
embodiment of the present invention.
[0049] FIG. 38 is a diagram illustrating the band-pass properties
of the band restricting filter shown in FIG. 37.
[0050] FIG. 39 is a diagram illustrating the spectral properties of
discrete narrow-band frame sequence light obtained by the band
restricting filter shown in FIG. 38.
[0051] FIG. 40 is a diagram illustrating the band-pass properties
of a first modification made on the band restricting filter shown
in FIG. 37.
[0052] FIG. 41 is a diagram illustrating the spectral properties of
discrete narrow-band frame sequence light from the band restricting
filter shown in FIG. 40.
[0053] FIG. 42 is a diagram illustrating the band-pass properties
of a second modification made on the band restricting filter shown
in FIG. 37.
[0054] FIG. 43 is a diagram illustrating an example of spectral
properties of the xenon lamp shown in FIG. 37.
[0055] FIG. 44 is a diagram illustrating the band-pass properties
of a third modification made on the band restricting filter shown
in FIG. 37, in the event that the spectral properties of the xenon
lamp are those shown in FIG. 43.
[0056] FIG. 45 is a configuration diagram illustrating the
configuration of a modification made on the light source device
shown in FIG. 37.
[0057] FIG. 46 is a diagram illustrating the configuration of the
light reduction rotating filter shown in FIG. 45.
[0058] FIG. 47 is a configuration diagram illustrating the
configuration of an endoscope device according to a fourth
embodiment of the present invention.
[0059] FIG. 48 is a diagram illustrating an example of spectral
distribution of light irradiated from the light source device shown
in FIG. 47 at the time of normal observation.
[0060] FIGS. 49a-d are diagrams illustrating the illumination
timing of each band by the electric power supply unit shown in FIG.
47, and the light quantity control timing at that time.
[0061] FIG. 50 is a diagram illustrating an example of the spectral
distribution of light irradiated from the light source device by
the electric power supply unit shown in FIG. 47, at the time of
narrow-band observation.
[0062] FIG. 51 is a configuration diagram illustrating the
configuration of an endoscope device according to a fifth
embodiment of the present invention.
[0063] FIG. 52 is a configuration diagram illustrating the
configuration of an endoscope device according to a sixth
embodiment of the present invention.
[0064] FIG. 53 is a configuration diagram illustrating the
configuration of an endoscope device according to a seventh
embodiment of the present invention.
[0065] FIG. 54 is a configuration diagram illustrating the
configuration of the light mixing unit shown in FIG. 53.
[0066] FIG. 55 is a diagram illustrating an example of spectral
distribution of the xenon lamp shown in FIG. 53.
[0067] FIG. 56 is a diagram illustrating an example of spectral
distribution of the extra-high pressure mercury lamp shown in FIG.
53.
[0068] FIG. 57 is a diagram illustrating an example of spectral
distribution of light irradiated from the light source device at
the time of narrow-band observation performed by the light mixing
unit shown in FIG. 54.
[0069] FIG. 58 is a configuration diagram illustrating the
configuration of an endoscope device according to an eighth
embodiment of the present invention.
[0070] FIG. 59 is a configuration diagram illustrating the
configuration of an endoscope device according to a ninth
embodiment of the present invention.
[0071] FIG. 60 is a diagram illustrating an adapter having a band
restricting filter which is mountable in the tip of the electronic
endoscope shown in FIG. 59.
[0072] FIG. 61 is a configuration diagram illustrating the
configuration of an endoscope device according to a tenth
embodiment of the present invention.
[0073] FIG. 62 is a configuration diagram illustrating the
configuration of the rotating filter shown in FIG. 61.
[0074] FIG. 63 is a diagram illustrating the spectral properties of
a first filter set of the rotating filter shown in FIG. 62.
[0075] FIG. 64 is a diagram illustrating the spectral properties of
a second filter set of the rotating filter shown in FIG. 62.
[0076] FIG. 65 is a diagram illustrating the structure of the
living body tissue to be observed with the endoscope device shown
in FIG. 61, in the layer direction.
[0077] FIG. 66 is a diagram describing the state of the
illumination light from the endoscope device shown in FIG. 61
reaching the living body tissue in the layer direction.
[0078] FIGS. 67a-c are diagrams illustrating each of the band
images from frame sequence light transmitted through the first
filter set shown in FIG. 63.
[0079] FIGS. 68a-c are diagrams illustrating each of the band
images from frame sequence light transmitted through the second
filter set shown in FIG. 64.
[0080] FIG. 69 is a diagram describing light adjustment control by
a light adjusting circuit shown in FIG. 61.
[0081] FIG. 70 is a configuration diagram illustrating the
configuration of the image processing circuit shown in FIG. 61.
[0082] FIG. 71 is a diagram illustrating a color image of a
narrow-band RGB image obtained by the image processing circuit
shown in FIG. 70.
[0083] FIG. 72 is a diagram describing the creation of a matrix
such that an average color tone is maintained in the 3.times.3
matrix circuit shown in FIG. 70.
[0084] FIG. 73 is a diagram illustrating an example of settings of
the LUT shown in FIG. 70.
[0085] FIG. 74 is a configuration diagram illustrating the
configuration of a modification made to the color conversion
processing circuit shown in FIG. 70.
[0086] FIG. 75 is a configuration diagram illustrating the
configuration of an endoscope device according to an eleventh
embodiment of the present invention.
[0087] FIG. 76 is a configuration diagram illustrating the
configuration of the image processing circuit shown in FIG. 75.
[0088] FIG. 77 is a configuration diagram illustrating the
configuration of the color adjusting circuit shown in FIG. 75.
[0089] FIG. 78 is a diagram illustrating the concept of hue and
saturation on a L*a*b* color space in the color adjusting circuit
shown in FIG. 75.
[0090] FIG. 79 is a configuration diagram illustrating the
configuration of an endoscope device according to a twelfth
embodiment of the present invention.
[0091] FIG. 80 is a configuration diagram illustrating the
configuration of the rotating filter shown in FIG. 79.
[0092] FIG. 81 is a diagram illustrating the spectral transmission
properties of the filters G2, B2a, and B2b, of the rotating filter
shown in FIG. 80.
[0093] FIG. 82 is a configuration diagram illustrating the
configuration of the band selecting circuit shown in FIG. 79.
[0094] FIG. 83 is a configuration diagram illustrating the
configuration of a modification made on the rotating filter shown
in FIG. 79.
[0095] FIG. 84 is a diagram illustrating spectral transmission
properties of the rotating filter shown in FIG. 83.
[0096] FIG. 85 is a configuration diagram illustrating the
configuration of an endoscope device according to a thirteenth
embodiment of the present invention.
[0097] FIG. 86 is a configuration diagram illustrating the
configuration of the rotating filter shown in FIG. 85.
[0098] FIG. 87 is a diagram illustrating the spectral properties of
the first filter set of the rotating filter shown in FIG. 86.
[0099] FIG. 88 is a diagram illustrating the spectral properties of
the second filter set of the rotating filter shown in FIG. 86.
[0100] FIG. 89 is a diagram illustrating the structure of the
living body tissue in the layer direction to be observed with the
endoscope device shown in FIG. 85.
[0101] FIG. 90 is a diagram describing the state of the
illumination light from the endoscope device shown in FIG. 85
reaching the living body tissue in the layer direction.
[0102] FIGS. 91a-c are diagrams illustrating each of the band
images from frame sequence light transmitted through the first
filter set shown in FIG. 87.
[0103] FIGS. 92a-c are diagrams illustrating each of the band
images from frame sequence light transmitted through the second
filter set shown in FIG. 88.
[0104] FIG. 93 is a diagram describing light adjustment control
performed by a light adjusting circuit shown in FIG. 85.
[0105] FIG. 94 is a configuration diagram illustrating the
configuration of the image processing circuit shown in FIG. 85.
[0106] FIG. 95 is a configuration diagram illustrating the
configuration of an endoscope device according to a fourteenth
embodiment of the present invention.
[0107] FIG. 96 is a configuration diagram illustrating the
configuration of the image processing circuit shown in FIG. 95.
[0108] FIG. 97 is a configuration diagram illustrating the
configuration of the filtering execution unit shown in FIG. 96.
[0109] FIG. 98 is a diagram illustrating the filter frequency
properties of the filtering execution unit shown in FIG. 97.
[0110] FIG. 99 is a diagram illustrating RGB images captured when
the narrow-band observation mode in FIG. 95.
[0111] FIG. 100 is a configuration diagram illustrating the
configuration of an image processing circuit according to a
fifteenth embodiment of the present invention.
[0112] FIG. 101 is a diagram illustrating a tone correction table
in the pre-processing unit in FIG. 100.
[0113] FIG. 102 is a diagram illustrating histogram distribution
applied to edge extraction processing performed by the edge
extraction processing unit shown in FIG. 100.
[0114] FIG. 103 is a diagram describing processing performed by the
pattern extraction unit shown in FIG. 100.
BEST MODE FOR CARRYING OUT THE INVENTION
[0115] The following is a description of the embodiments of the
present invention with reference to the drawings.
[0116] First, a first embodiment of the present invention will be
described with reference to FIG. 1 through FIG. 33. Here, FIG. 1 is
a configuration diagram illustrating the configuration of an
endoscope device, FIG. 2 is a configuration diagram illustrating
the configuration of a rotating filter shown in FIG. 1, FIG. 3 is a
diagram illustrating the spectral properties of a first filter set
of the rotating filter shown in FIG. 2, FIG. 4 is a diagram
illustrating the spectral properties of a second filter set of the
rotating filter shown in FIG. 2, FIG. 5 is a diagram illustrating
the structure of the living body tissue in the layer direction to
be observed with the endoscope device shown in FIG. 1, FIG. 6 is a
diagram describing the state of the illumination light from the
endoscope device shown in FIG. 1 reaching the living body tissue in
the layer direction, FIG. 7 is a diagram illustrating each of the
band images from frame sequence light transmitted through the first
filter set shown in FIG. 3, FIG. 8 is a diagram illustrating each
of the band images from frame sequence light transmitted through
the second filter set shown in FIG. 4, FIG. 9 is a diagram
describing light adjustment control performed by a light adjusting
circuit shown in FIG. 1, FIG. 10 is a diagram illustrating the
spectral properties of a first modification made on the second
filter set of the rotating filter shown in FIG. 2, FIG. 11 is a
diagram illustrating the spectral properties of a second
modification made on the second filter set of the rotating filter
shown in FIG. 2, FIG. 12 is a diagram illustrating the spectral
properties of a third modification made on the second filter set of
the rotating filter shown in FIG. 2, FIG. 13 is a diagram
describing the operations of a third modification made on the
second filter set of the rotating filter shown in FIG. 2, FIG. 14
is a diagram illustrating a first example of spectral distribution
of a xenon lamp shown in FIG. 1, FIG. 15 is a diagram illustrating
the spectral properties of a fourth modification made on the second
filter set of the rotating filter in the event that the spectral
distribution of the xenon lamp shown in FIG. 14 is applied, FIG. 16
is a diagram illustrating spectral properties of living body tissue
illumination light with the fourth modification made on the second
filter set shown in FIG. 14, FIG. 17 is a diagram illustrating a
second example of spectral distribution of the xenon lamp shown in
FIG. 1, FIG. 18 is a diagram illustrating an example of spectral
sensitivity properties of the CCD shown in FIG. 1, FIG. 19 is a
diagram illustrating the spectral properties of a light reduction
filter to be applied by vapor deposition to a fifth modification
made on the second filter set of the rotating filter in the event
that the spectral distribution of the xenon lamp is that in the
second example and the spectral sensitivity properties of the CCD
are those shown in FIG. 18, FIG. 20 is a diagram illustrating the
spectral properties of the fifth modification made on the second
filter set to which the light reduction filter shown in FIG. 19 has
been applied by vapor deposition, FIG. 21 is a configuration
diagram illustrating a first modification of the light source
device shown in FIG. 1, FIG. 22 is a configuration diagram
illustrating the configuration of the light reduction rotating
filter shown in FIG. 21, FIG. 23 is a configuration diagram
illustrating the configuration of a second modification made on the
light source device shown in FIG. 1, FIG. 24 is a diagram
illustrating the light reduction properties of a first light
reduction filter making up the light reduction filter shown in FIG.
23, FIG. 25 is a diagram illustrating the light reduction
properties of a second light reduction filter making up the light
reduction filter shown in FIG. 23, FIG. 26 is a diagram
illustrating the light reduction properties of the light reduction
filter shown in FIG. 23, FIG. 27 is a diagram illustrating an
example illustrating detailed spectral properties of the second
filter set of the rotating filter shown in FIG. 2, FIG. 28 is a
diagram illustrating the spectral properties of a sixth
modification made on the second filter set of the rotating filter
shown in FIG. 2, FIG. 29 is a diagram illustrating the
configuration of the principal components of a modification made on
the video processor shown in FIG. 1, FIG. 30 is a first diagram
describing the operations of the video processor shown in FIG. 29,
FIG. 31 is a second diagram describing the operations of the video
processor shown in FIG. 29, FIG. 32 is a diagram illustrating the
spectral properties of a seventh modification made on the second
filter set of the rotating filter shown in FIG. 2, and FIG. 33 is a
diagram illustrating the spectral properties of the seventh
modification made on the second filter set shown in FIG. 32.
[0117] As shown in FIG. 1, the endoscope device 1 according to the
present embodiment is configured of an electronic endoscope 3 which
is inserted inside the body cavity and which has a CCD 2 serving as
image-pickup means for capturing images of tissue within the body
cavity, a light source device 4 for supplying illumination light to
the electronic endoscope 3, and a video processor 7 for subjecting
image-pickup signals from the CCD 2 of the electronic endoscope 3
to signal processing and displaying endoscopic images on an
observation monitor 5 or encoding the endoscopic images and
outputting to an image filing device 6 as compressed images.
[0118] The light source device 4 is configured of a xenon lamp 11
for emitting illumination light, a heat ray cut filter 12 for
shielding heat rays from the white light, a diaphragm device 13 for
controlling the light quantity of the white light through the heat
ray cut filter 12, a rotating filter 14 for turning the
illumination light into frame sequence light, a condenser lens 16
for collecting the frame sequence light coming through the rotating
filter 14 onto the incident face of a light guide 15 disposed
within the electronic endoscope 3, and a control circuit 17 for
controlling the rotation of the rotating filter 14.
[0119] As shown in FIG. 2, the rotating filter 14 is formed in a
disk-like shape and has a double structure with the center as the
rotating axis, wherein an R1 filter 14r1, a G1 filter 14g1, and a
B1 filter 14b1 making up a first filter set for outputting frame
sequence light having overlapping spectral properties suitable for
color reproduction such as indicated in FIG. 3 are situated on the
outer sector, and wherein an R2 filter 14r2, a G2 filter 14g2, and
a B2 filter 14b2 making up a second filter set for outputting
narrow-band frame sequence light having discrete spectral
properties enabling extraction of desired deep tissue information
such as indicated in FIG. 4 are situated on the inner sector. As
shown in FIG. 1, the rotating filter 14 is rotated by the control
circuit 17 performing driving control of a rotating filter motor
18, and movement in the radial direction (movement which is
perpendicular to the optical path of the rotating filter 14, which
is selectively moving the first filter set or second filter set of
the rotating filter 14 onto the optical path) is performed by a
mode switch-over motor 19 based on control signals from a mode
switch-over circuit 42 within the later-described video processor
7.
[0120] Note that electric power is supplied to the xenon lamp 11,
diaphragm device 13, rotating filter motor 18, and mode switch-over
motor 19, from the electric power supply unit 10.
[0121] Returning to FIG. 1, the video processor 7 is configured
comprising a CCD driving circuit 20 for driving the CCD 2, an
amplifier 22 for amplifying image-pickup signals wherein images are
captured in the body cavity tissue by the CCD 2 through an
objective optical system 21, a process circuit 23 for performing
correlated double sampling and noise reduction and so forth, with
regard to image-pickup signals coming through the amplifier 22, an
A/D converter 24 for converting the image-pickup signals passing
through the process circuit 23 into image data of digital signals,
a white balance circuit 25 for subjecting the image data from the
A/D converter 24 to white balance processing, a selector 26 and
synchronizing memories 27, 28, and 29, for synchronizing the frame
sequence light from the rotating filter 14, an image processing
circuit 30 for reading out each set of image data of the frame
sequence light stored in the synchronizing memories 27, 28, 29, and
subjecting these to gamma correction processing, outline
enhancement processing, color processing, etc., D/A circuits 31,
32, and 33, for converting the image data from the image processing
circuit 30 into analog signals, an encoding circuit 34 encoding the
output of the D/A circuits 31, 32, and 33, and a timing generator
35 for inputting synchronizing signals synchronized with the
rotation of the rotating filter 14 from the control circuit 17 of
the light source device 4, and outputting various types of timing
signals to the above-described circuits.
[0122] Also, a mode switch-over switch 41 is provided in the
electronic endoscope 2, with the output of this switch-over switch
41 being output to the mode switch-over circuit 42 within the video
processor 7. The mode switch-over circuit 42 of the video processor
7 makes output of control signals to a light adjusting circuit 43,
a light adjustment control parameter switch-over circuit 44, and
the mode switch-over motor 19 of the light source 4. The light
adjustment control parameter switch-over circuit 44 outputs light
adjustment control parameters corresponding to the first filter set
or second filter set of the rotating filter 14 to the light
adjusting circuit 43, and the light adjusting circuit 43 controls
the diaphragm device 13 of the light source device 4 based on the
control signals from the mode switch-over circuit 42 and light
adjusting parameters from the light adjustment control parameter
switch-over circuit 44, so as to perform appropriate brightness
control.
[0123] Next, the operations of the endoscope device according to
the present embodiment configured thus will be described.
[0124] As shown in FIG. 5, a body cavity tissue 51 often has a
structure wherein there is a distribution of different absorbent
material such as blood vessels in the depth direction, for example.
There is primarily a greater distribution of capillaries 52 near
the surface of mucus membranes, blood vessels 53 which are thicker
than the capillaries are also distributed along with the
capillaries at the middle layer which is deeper than this layer,
and even thicker blood vessels 54 are distributed at even deeper
layers.
[0125] On the other hand, the permeation depth of the light in the
depth direction as to the body cavity tissue 51 is dependent on the
wavelength of light, and with illumination light containing the
visible region, as shown in FIG. 6, in the case of light with a
short wavelength such as blue (B), the light only reaches around
the surface layer due to the absorption properties and scattering
properties at the living body tissue, being subjected to absorption
and scattering within the range up to that depth, so light coming
out from the surface is observed. Also, in the case of green (G)
light with a wavelength longer than that of blue (B) light, the
light reaches a depth deeper than the range where the blue (B)
light reaches, is subjected to absorption and scattering within the
range at that depth, and light coming out from the surface is
observed. Further, red (R) light with a wavelength longer than that
of green (G) light, reaches a range even deeper.
[0126] At the time of performing normal observation, the mode
switch-over motor 19 is controlled by the mode switch-over circuit
within the video processor 7 with control signals, so that the R1
filter 14r1, G1 filter 14g1, and B1 filter 14b1, making up the
first filter set of the rotating filter 14, are positioned on the
optical path of the illumination light.
[0127] With the R1 filter 14r1, G1 filter 14g1, and B1 filter 14b1,
the wavelength regions are each overlapped as shown in FIG. 3, so
at the time of normal observation of the body cavity tissue 51, a
band image having shallow layer and middle layer tissue information
containing a great amount of tissue information at the shallow
layer such shown in "a" in FIG. 7 is captured in the image-pickup
signals taken by the CCD 2 with the B1 filter 14b1, a band image
having shallow layer and middle layer tissue information containing
a great amount of tissue information at the middle layer such as
shown in "b" in FIG. 7 is captured in the image-pickup signals
taken by the CCD 2 with the G1 filter 14g1, and further, a band
image having middle layer and deep layer tissue information
containing a great amount of tissue information at the deep layer
such shown in "c" in FIG. 7 is captured in the image-pickup signals
taken by the CCD 2 with the R1 filter 14r.
[0128] These RGB image-pickup signals are synchronized with the
video processor 7 and subjected to signal processing, thus enabling
an endoscopic image with desired or natural color reproduction to
be obtained as an endoscopic image.
[0129] On the other hand, upon the mode switch-over switch 41 of
the electronic endoscope 3 being pressed, the signals thereof are
input to the mode switch-over circuit 42 of the video processor 7.
The mode switch-over circuit 42 outputs control signals to the mode
switch-over motor 19 of the light source device 4, thereby moving
the first filter set of the rotating filter 14 that was on the
optical path at the time of normal observation, and drives the
rotating filter 14 with regard to the optical path so that the
second filter set is positioned upon the optical path.
[0130] In the event of performing narrow-band light observation of
the body cavity tissue 51 with the second filter set, the R2 filter
14r2, G2 filter 14g2, and B2 filter 14b2 make the illumination
light to be narrow-band frame sequence light with discrete spectral
properties as shown in FIG. 4, so a band image having tissue
information at a shallow layer such as shown in "a" in FIG. 8 is
captured in the image-pickup signals taken by the CCD 2 with the B2
filter 14b2, a band image having tissue information at the middle
layer such as shown in "b" in FIG. 8 is captured in the
image-pickup signals taken by the CCD 2 with the G2 filter 14g2,
and a band image having tissue information at the deep layer such
as shown in "c" in FIG. 8 is captured in the image-pickup signals
taken by the CCD 2 with the R2 filter 14r2.
[0131] As can be clearly understood from FIG. 3 and FIG. 4, at this
time, the quantity of transmitted light from the second filter set
is less than the quantity of transmitted light from the first
filter set, because the bands thereof are narrowed, so the light
adjusting circuit 43 controls the diaphragm device 13 by outputting
light adjustment control parameters according to the first filter
set or second filter set of the rotating filter 14, from the light
adjustment control parameter switch-over circuit 44 to the light
adjusting circuit 43, thereby, as shown in FIG. 9, controlling the
diaphragm device 13 when making narrow-band light observation so as
to control light quantity Mx with a diaphragm control curve 62
corresponding to a set value Lx, with respect to, for example, a
linear diaphragm control line 61 by the diaphragm device 13 in
normal observation, corresponding to the set value Lx on an unshown
setting panel of the video processor 7.
[0132] Specifically, the aperture level value corresponding to the
light quantity setting value Lx changes from Mx1 to Mx2 as shown in
FIG. 9, being interlocked with changing the first filter set to the
second filter set, and consequently, the diaphragm is controlled in
the direction of being opened, and acts to compensate for reduction
in the quantity of illumination light by the filter which narrows
the band.
[0133] Thus, image data with sufficient brightness can be obtained
even when making narrow-band light observation.
[0134] Thus, according to the present embodiment, a transfer to
narrow-band light observation can be made by pressing the mode
switch-over switch 41 as necessary so as to switch from the first
filter set of the rotating filter 14 to the second filter set while
performing normal observation of the body cavity tissue 51, and in
this narrow-band light observation, each of the layers of the body
cavity tissue 51 can be obtained as image-pickup signals in the
state of the living body tissue of each being separated by the
second filter set of the rotating filter 14, and also image-pickup
signals of a suitable light quantity can be obtained by controlling
the diaphragm device 13, so tissue information about each of the
layers of the body cavity tissue 51 which is important for
diagnosis can be visually recognized in a sure manner and can be
diagnosed in a more accurate manner.
[0135] Now, while the second filter set has been made to be a
filter set with illumination light spectrum properties such as
shown in FIG. 4 (R2 filter 14r2, G2 filter 14g2, and B2 filter
14b2), the invention is not restricted to this, and as a first
modification of the second filter set, the second filter may be a
filter set which generates narrow-band frame sequence light with
discrete spectral properties as shown in FIG. 10, for example, from
the illumination light. With the filter set according to this first
modification, the G filter and R filter are the same as the G
filter and the R filter of the first filter set, and only the B
filter carries a narrow bandwidth. This modification is
particularly suitable for cases wherein there is interest in the
capillaries structures and the like near the surface of the living
body tissue, and conventional images suffice for the other band
images.
[0136] Also, the filter properties are not restricted to visible
light, and as a second modification of the second filter set, the
second filter may be a filter set which generates narrow-band frame
sequence light with discrete spectral properties as shown in FIG.
11, for example, from the illumination light. This filter set
according to the second modification is suitable for obtaining any
image information not applicable with normal observation, by
setting B to the near-ultraviolet region and R to the near-infrared
region, in order to observe the irregular portions at the surface
of the organism and absorbents at extremely deep layers.
[0137] Further, as the third modification of the second filter set,
the second filter may be a filter set comprising two filters B2a
and B2b which come close at the near-wavelength region, instead of
the G filter, as shown in FIG. 12. This is suitable for visualizing
minute differences in scattering properties rather than absorption
properties, using the fact that the wavelength bandwidth in this
area only permeates to around the extreme surface layer of the
organism. That is, as shown in FIG. 13, configuring the filter at a
position where the scattering properties greatly change such that
the absorption properties of the organism are approximately equal
at the center wavelength of B2a and B2b is suitable for visualizing
scattering properties near the surface. Medically, application can
be envisioned for diagnosis for recognizing disorders involving
disarray in cell arrays near the surface of mucous membranes, such
as for early cancer or the like.
[0138] Also, generally, xenon lamps and the like are often
manufactured so as to shield ultraviolet light. FIG. 14 shows an
example of spectral distribution of the illumination light source.
Accordingly, with the B region in the second filter set, even in
the event that the short wavelength side is given open properties
as a transmitting area as shown in FIG. 15, the properties are as
such as shown in FIG. 16 in the combination with a spectral
properties of the light source, and consequently, narrow-band
illumination light properties can be realized. Also, manufacturing
of the optical filter is normally often performed by vapor
deposition of a multi-layer interference film filter, and with that
manufacturing method, the vapor deposition in with many layers of
film must be performed in order to yield narrow-band for the
spectral transmissivity properties thereof, resulting in increased
costs and thicker filters, but the manufacturing costs and
thickness can be reduced by using the lump properties in this way
and giving open properties to one side.
[0139] Also, in the event that the spectral distribution of the
light source are such as shown in FIG. 17, or in the event that the
spectral sensitivity properties of the CCD are as shown in FIG. 18,
the light adjustment is set somewhat brighter to compensate for the
reduction in light quantity by narrowing the bandwidth, in
association with switching over from the first filter set of the
rotating filter 14 to the second filter set, and consequently it
can be conceived that the B2 band image is suitable, but that the
G2 band image and R2 band image tend to be saturated. Or, the white
balance is adjusted at the white balance circuit 25 shown in FIG.
1, and consequently, the B2 band image with a low brightness level
is excessively amplified by the second filter set, light source
device, and CCD sensitivity properties, resulting in an image with
poor SN being observed.
[0140] Accordingly, it is necessary to control not only the
bandwidth properties but also the peak transmittance properties as
well, taking into consideration factors which affect the system
spectral sensitivity, such as light source spectral distribution
properties, CCD spectral sensitivity properties, and so forth.
[0141] Accordingly, taking into consideration the system spectral
sensitivity properties other than filter, and light adjustment
properties, an arrangement may be configured as the fifth
modification of the second filter set, wherein a light reducing
filter having light reducing properties "a" and "b" as shown in
FIG. 19 is vapor-deposited or adhered to the R2 filter 14r2 or G2
filter 14g2 of the rotating filter 14 to obtain an image with
suitable brightness. Consequently, a narrow-band filter set having
properties such as shown in FIG. 20, can be obtained. In this way,
not only the bandwidth properties, but also the transmissivity
properties thereof can also be suitably set, so images with optimal
brightness for each band can be observed.
[0142] As a method for controlling not only bandwidth properties
but also peak transmissivity properties, taking into consideration
factors which affect the system spectral sensitivity, such as light
source spectral distribution properties, CCD spectral sensitivity
properties, and so forth, a configuration may be made wherein, in
addition to a light reducing filter being vapor-deposited or
adhered to the R2 filter 14r2 and G2 filter 14g2 of the rotating
filter 14 as described above, a first modification of the light
source device 4 as shown in FIG. 21 may comprise a light reducing
rotating filter 61 provided all the optical path, separate from the
rotating filter 14. As shown in FIG. 22, this light reducing
rotating filter 61 has the same double structure as the rotating
filter 14 (see FIG. 2) and, with the portions corresponding to the
R1 filter 14r1, G1 filter 14g1, B1 filter 14b1, and B2 filter 14b2
of the rotating filter 14 being transmitting portions, and
comprising light reducing filters 62 and 63 for reducing the light
of the bandwidth portions corresponding only to the R2 filter 14r2
and G2 filter 14g2, respectively. The light reducing rotating
filter 61 is rotationally driven by a rotating filter motor 64
based on control signals of the control circuit 17 in the same way
as the rotating filter 14, and also is capable of motion
perpendicular to the optical path in the radial direction thereof
by a mode switch-over motor 65 based on control signals from the
mode switch-over circuit 42, and the driving timing thereof is
carried out synchronously with the rotating filter 14.
[0143] Also, as a method for controlling not only bandwidth
properties but also peak transmissivity properties, taking into
consideration factors which affect the system spectral sensitivity,
such as light source spectral distribution properties, CCD spectral
sensitivity properties, and so forth, a second modification of the
light source device 4 comprises a light reducing filter 71, instead
of the light source device comprising the light reducing rotating
filter 61 as described above. The light reducing filter 71 has
desired bandwidth transmissivity by combination of multiple filters
and is insertable to and extractable from the optical path by a
filter driving motor 72 based on control signals from the mode
switch-over circuit 42, the driving thereof being extracted at the
time of the first filter of the rotating filter 14, and inserted at
the time of the second filter, as shown in FIG. 23. This light
reducing filter 71 is capable of controlling not only bandwidth
properties but also peak transmissivity properties, by having light
reducing properties such as shown in FIG. 26, by combining, for
example, a first light reducing filter having light reducing
properties shown in FIG. 24 and a second light reducing filter
having light reducing properties shown in FIG. 25.
[0144] Now, as for an example of specific spectral properties of
the above-described R2 filter 14r2, G2 filter 14g2, and B2 filter
14b2, as shown in FIG. 27, the R2 filter 14r2 has band-pass
properties including 600 nm for the wavelength bandwidth and 20 to
40 nm for a full width at half maximum, the G2 filter 14g2 has
band-pass properties including 540 nm for the wavelength bandwidth
and 20 to 40 nm for a full width at half maximum, and further the
B2 filter 14b2 has band-pass properties including 420 nm for the
wavelength bandwidth and 20 to 40 nm for a full width at half
maximum.
[0145] With the spectral properties such as shown in FIG. 27, the
capillary structure on the mucous membrane surface can be
reproduced in high contrast by making the observation with an
illumination light having narrow-band properties including 420 nm
which is the band at which absorption of blood by visible light is
great, and further, the distribution in the depth direction of the
absorbents within the body mucous membrane can be reproduced with a
different color, so the relative position of the absorbents other
than the blood vessel images and the like in the depth direction
can be conceptualized.
[0146] Also, as a modification made on the above-described R2
filter 14r2, G2 filter 14g2, and B2 filter 14b2, the G' filter
14g', G'' filter 14g'', and B2 filter 14b2 shown in FIG. 28 may be
used, wherein the G' filter 14g' has band-pass properties including
550 nm for the wavelength bandwidth and 20 to 40 nm for a full
width at half maximum, the G'' filter 14g'' has band-pass
properties including 500 nm for the wavelength bandwidth and 20 to
40 nm for a full width at half maximum, and further the B2 filter
14b2 has band-pass properties including 420 nm for the wavelength
bandwidth and 20 to 40 nm for a full width at half maximum.
[0147] With the spectral properties such as shown in FIG. 28, the
capillary structure on the mucous membrane surface can be
reproduced in high contrast by making the observation with an
illumination light having narrow-band properties including 420 nm
which is the band at which absorption of blood by visible light is
great, and further, providing band-pass light around 500 nm which
is the neighboring bandwidth can realize image reproduction
specialized for the structure of the mucous membrane surface.
[0148] Also, the aperture level value corresponding to the light
quantity setting value Lx is changed from Mx1 to Mx2 as shown in
FIG. 9, being interlocked with the change from the first filter set
to the second filter set, and consequently, the diaphragm is
controlled in the direction of being opened, acting to compensate
for reduction in the illumination light quantity by the filter
which narrows the band, but the exposure time may be extended to
increase the irradiated light quantity.
[0149] However, the organism which is the subject is not
necessarily stationary, and does have peristalsis and pulse, so
performing freezing operations while observing the image means that
the image moves while exposing the CCD, and increases in the
irradiated light quantity by extending this exposure time, and thus
creates problems in that shaking of the image increases.
[0150] Accordingly, as a modification of the video processor 7,
memories 180, 181, and 182 for pre-freezing, for constantly
recording several frames of images, are provided after the
synchronizing memories 27, 28, and 29, and a motion detecting
circuit 190 for detecting motion by comparing image data between
fields by the output signals of the synchronizing memories 27, 28,
and 29, and the input signals of the selector 26, is provided, as
shown in FIG. 29.
[0151] Due to such a configuration, pressing the mode switch-over
switch 41 provided on the electronic endoscope 3 controls the
rotation of the rotating filter 14 so that the mode switch-over
circuit 42 controls the timing generator 35 such that the exposure
time is made to be twice that of normal observation time by the
control circuit 17 of the light source device 4 (the rotating speed
for the second filter set of the rotating filter 14 is made to be a
half of the rotating speed of the first filter set).
[0152] Also, in the event that a freeze switch 185 provided in the
electronic endoscope 3 is pressed, image data is compared between
fields by a motion detecting circuit 190 so as to detect motion, at
the timing shown in FIG. 30 at the time of normal observation, and
at the timing shown in FIG. 31 at the time of narrow-band
observation, thereby controlling updating of the image data to be
recorded in the memories 180, 181, and 182.
[0153] Specifically, taking a normal observation time shown in FIG.
30 as an example for description, image data R0 of one field period
stored in the synchronizing memory 27 is compared with image data
G0 input from the selector 26 by the motion detecting circuit 190
(the first comparison), and further image data G0 of one field
period stored in the synchronizing memory 28 is compared with image
data B0 input from the selector 26 (the second comparison), and in
the event that judgment is made that there are no movements between
either, the mode switch-over circuit 42 controls the timing
generator 35, and then in the next field period (the period denoted
by an asterisk in the figure), the image data R0, G0, and B0,
stored in the synchronizing memories 27, 28, and 29, is written to
the memories 180, 181, and 182.
[0154] Also, following judgment that there is no motion as the
result of the above second comparison by the motion detecting
circuit 190, image data B0 of one field period stored in the
synchronizing memory 29 is compared with image data R1 input from
the selector 26 (the third comparison), and in the event that
judgment is made that there is no movement as the results of the
third comparison as well, the mode switch-over circuit 42 controls
the timing generator 35, and then in the next field period (the
period denoted by a star in the figure), the image data R1, G0, and
B0, stored in the synchronizing memories 27, 28, and 29, is
overwritten on the memories 180, 181, and 182.
[0155] Also, in the event that judgment is made there is movement
as the result of the third comparison, there is no updating in the
above-described period denoted by a star, and the data recorded in
the above period is kept in the memories 180, 181, and 182.
[0156] Thus, updating of the memories 180, 181, and 182 is
sequentially performed at the subsequent field. Also, the same
updating is performed for the memories 180, 181, and 182, with
narrow-band observation as well, except that the exposure time is
doubled, as shown in FIG. 31.
[0157] Upon the freeze switch 185 provided in the electronic
endoscope 3 being pressed, the mode switch-over circuit 42 controls
the timing generator 35 to stop the reading out from the
synchronizing memories 27, 28, and 29, and the image data read out
from the memories 180, 181, and 182 is output to the image
processing circuit 30.
[0158] However, in the event that there is no image data in the
memories 180, 181, and 182, or immediately following the mode
switch-over switch 41 being pressed and switching over having been
made to the second filter set of the rotating filter 14, the
reading out from the synchronizing memories 27, 28, and 29,
continues even if the freeze switch 185 is pressed, until motion is
detected by the motion detecting circuit 190, and reading out from
the synchronizing memories 27, 28, and 29, is stopped for the first
time upon motion being detected.
[0159] Providing the memories 180, 181, and 182 and the motion
detecting circuit 190 as shown in FIG. 29 allows images wherein
shaking is suppressed to a minimum to be obtained even in the event
of freezing in a state that the exposure time has been extended for
narrow-band observation.
[0160] Now, generally, florescent images of living body tissue from
excitation light do not reflect the fine structure of the surface
of mucous membranes, but do bring to light disorders which are not
readily discovered with visible light. On the other hand, the fine
structures of the surface of the mucous membranes, such as
capillary structure images, and so forth, are known to be crucial
information for differential diagnosis of disorders. Accordingly,
an arrangement may be made wherein these two types of information
are combined and displayed as an image, thereby improving
diagnostic capabilities.
[0161] Specifically, a second filter set of the rotating filter is
configured of an excitation light F filter 14f, and G2 filter 14g2
and B2 filter 14b2, as shown in FIG. 32, instead of the R2 filter
14r2, G2 filter 14g2, and B2 filter 14b2. Now, the spectral
properties with the excitation light F filter 14f are properties
such as shown in FIG. 33.
[0162] Upon irradiating narrow-band excitation light from the F
filter 14f onto the living body tissue, fluorescent light with the
wavelength such as shown in FIG. 33 is emitted from the living body
tissue. Accordingly, with the above-described embodiment, normal
observation giving weight to color reproduction properties has wide
band properties, and highly functional observation by fluorescent
light and narrow-band light superimposed, can be switched between
and applied.
[0163] In this way, observation of disorders which cannot be
readily discovered with visible light by florescent light
observation, and detailed observation of the surface of mucous
membranes by narrow-band light can be performed, thereby improving
diagnostic capabilities.
[0164] Next, a second embodiment of the present invention will be
described with reference to FIG. 34 through FIG. 36.
[0165] FIG. 34 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 35 is a configuration
diagram illustrating the configuration of the rotating filter shown
in FIG. 34, and FIG. 36 is a diagram illustrating the spectral
properties of the color chip shown in FIG. 34.
[0166] The second embodiment is almost the same as the first
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0167] As shown in FIG. 34, with the electronic endoscope 3
according to the present embodiment, a color chip 81 is disposed on
the front face of the CCD 2, thereby making up a color CCD 2a,
configuring an endoscope device 1 of a synchronous system when
performing normal observation. Color image signals from the color
CCD 2a are converted into color image data at the A/D converter 24,
subsequently subjected to color separation at a color separating
circuit 82, then input to the white balance circuit 25, and stored
in memories 83, 84, and 85, via the selector 26, subsequently
subjected to interpolation processing or the like at the image
processing circuit 30, following which desired image processing is
performed.
[0168] As shown in FIG. 35, the rotating filter 86 of the light
source device 4 is made up of an R2 filter 14r2, G2 filter 14g2,
and B2 filter 14b2, having spectral properties which are the same
as that of the second filter set in the first embodiment,
rotationally driven by the rotating filter motor 18 based on
control signals from the control circuit 17, and being insertable
to and extractable from the optical path by a filter driving motor
87 based on control signals from the mode switch-over circuit 42
which has received instruction signals from the mode switch-over
switch 41 provided in the electronic endoscope 3.
[0169] With the present embodiment thus configured, a rotating
filter 86 is extracted from the optical path at normal observation
time, so that white light is irradiated on the living body tissue.
The living body tissue image of the white light is captured by the
color CCD 2a. The spectral properties of the color chip 81 on the
front face of the CCD 2a at this time are shown in FIG. 36.
[0170] On the other hand, when making narrow-band like observation,
the rotating filter 86 is inserted into the optical path, with
frame sequence light from the R2 filter 14r2, G2 filter 14g2, and
B2 filter 14b2, irradiated to the living body tissue. A living body
tissue image of this frame sequence light is taken by the color CCD
2a.
[0171] Accordingly, frame sequence light having discrete
narrow-band spectral properties from the R2 filter 14r2, G2 filter
14g2, and B2 filter 14b2, is irradiated on to the body organism at
the time of narrow-band observation, so the same advantages as
those of the first embodiment can be obtained with the present
embodiment, as well.
[0172] Next, a third embodiment of the present invention will be
described with reference to FIG. 37 through FIG. 46.
[0173] FIG. 37 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 38 is a diagram
illustrating the band-pass properties of the band restricting
filter shown in FIG. 37, FIG. 39 is a diagram illustrating the
spectral properties of discrete narrow-band frame sequence light
obtained by the band restricting filter shown in FIG. 38, FIG. 40
is a diagram illustrating the band-pass properties of a first
modification made on the band restricting filter shown in FIG. 37,
FIG. 41 is a diagram illustrating the spectral properties of
discrete narrow-band frame sequence light from the band restricting
filter shown in FIG. 40, FIG. 42 is a diagram illustrating the
band-pass properties of a second modification made on the band
restricting filter shown in FIG. 37, FIG. 43 is a diagram
illustrating an example of spectral properties of the xenon lamp
shown in FIG. 37, FIG. 44 is a diagram illustrating the band-pass
properties of a third modification made on the band restricting
filter shown in FIG. 37, in the event that the spectral properties
of the xenon lamp are those shown in FIG. 43, FIG. 45 is a
configuration diagram illustrating the configuration of a
modification made on the light source device shown in FIG. 37, and
FIG. 46 is a diagram illustrating the configuration of the light
reduction rotating filter shown in FIG. 45.
[0174] The third embodiment is almost the same as the first
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0175] As shown in FIG. 37, the light source device 4 according to
the present embodiment comprises a rotating filter 91 upon which
are disposed an R1 filter 14r1, G1 filter 14g1, and B1 filter 14b1,
and a bandwidth redistricting filter 92 having multi-peak band-pass
properties (R2 band, G2 band, and B2 band), as shown in FIG. 38,
for restricting the bandwidth of transmitted light, where the
rotating filter 91 is rotationally driven by the rotating filter
motor 18 based on control signals from the control circuit 17, and
the bandwidth restricting filter 92 is insertable to and
extractable from the optical path by a filter driving motor 87
based on control signals from the mode switch-over circuit 42 which
has received the instruction signals from the mode switch-over
switch 41.
[0176] With the present embodiment thus configured, the bandwidth
restricting filter 92 is inserted into the optical path, whereby
the frame sequence light transmitting the rotating filter 91
becomes discrete narrow-band frame sequence light as shown in FIG.
39, and this narrow-band frame sequence light is irradiated on the
living body tissue, so the same advantages as those of the first
embodiment can be obtained with the present embodiment, as
well.
[0177] Now, with the present embodiment, the bandwidth restricting
filter 92 is configured to have narrow-band properties at the three
bands of RGB as shown in FIG. 38, but the embodiment is not
restricted to this, and in the event that improvement in only the
observation capabilities of the body surface structures is desired,
there is no need to make all three bands narrow bandwidth, rather,
only the B band needs to be narrow, so a bandwidth restricting
filter having irregular multi-peak band-pass properties may be used
as shown in FIG. 40, and combining such a bandwidth restricting
filter with the RGB rotating filter 91 allows frame sequence light
having narrow-band properties for the B band alone to be irradiated
onto the living body tissue, as shown in FIG. 41.
[0178] In order to provide the narrow-band properties for the B
band alone, the bandwidth restricting filter 92 may be made to be a
bandwidth restricting filter wherein the RGB light is made to be
light of B' alone, as shown in FIG. 42, with the specific example
of narrow-band properties of this B' alone being band-pass
properties including 420 nm for the wavelength bandwidth and 20 to
40 nm for a full width at half maximum.
[0179] With the spectral properties such as shown in FIG. 42, the
capillary structure on the mucous membrane surface can be
reproduced in high contrast by making the observation with an
illumination light having narrow-band properties including 420 nm
which is the band at which absorption of blood by visible light is
great.
[0180] Also, in the event that the shielding properties of the
short wavelength region side of the rotating filter 91 can be used,
such as in cases wherein the spectral properties of the xenon lamp
have properties of attenuation in the short wavelength region, as
shown in FIG. 43, a bandwidth restriction filter having open
properties instead of having band-pass properties at the short
wavelength side may be used, as shown in FIG. 44.
[0181] Also, taking into consideration the fact that energy for the
lamp drops in the short wavelength region, and further that the CCD
spectral sensitivity properties lose sensitivity in this region,
the gain of the B2 band image is excessively increased as a result
of color adjustments processing such as white balance and the like,
thereby yielding an image with a very great amount of noise.
[0182] Accordingly, as a modification of the light source device,
the light quantity for each band is adjusted at the light source
side so that each band image has appropriate SN properties even
after performing white balance taking into consideration the
spectral properties other than those of the filter, such as of the
lamp, CCD, etc., by inserting the light reducing rotating filter 95
into the optical path, as shown in FIG. 45.
[0183] That is, as shown in FIG. 46, each part of the light
reducing rotating filter 95 corresponding to the B1 filter 14b1 of
the rotating filter 91 is configured as a transmitting portion, and
the parts corresponding to the R1 filter 14r1 and the G1 filter
14g1 are configured as light reducing filters for reducing the
light of the corresponding bandwidths. The light reducing rotating
filter 95 is rotationally driven by a rotating filter motor 96
based on control signals from the control circuit 17 in the same
way as the rotating filter 91, and also is capable of moving
perpendicularly to the optical path in the radial direction thereof
by a mode switch-over motor 97 based on controls signals from the
mode switch-over circuit 42, and the driving timing thereof is
carried out synchronously with that of the rotating filter 91.
[0184] Next, a fourth embodiment of the present invention will be
described with reference to FIG. 47 to FIG. 50.
[0185] FIG. 47 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 48 is a diagram
illustrating an example of spectral distribution of light
irradiated from the light source device shown in FIG. 47 at the
time of normal observation, FIG. 49 is a diagram illustrating the
illumination timing of each band by the electric power supply unit
shown in FIG. 47, and the light quantity control timing at that
time, and FIG. 50 is a diagram illustrating an example of the
spectral distribution of light irradiated from the light source
device by the electric power supply unit shown in FIG. 47, at the
time of narrow-band observation.
[0186] The fourth embodiment is almost the same as the third
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0187] With the light source device according to the present
embodiment, the electric power unit 10 is capable of receiving
control signals from the light adjusting circuit 43 and changing
the driving voltage of the xenon lamp 11.
[0188] Taking the lamp properties into consideration, the spectral
distribution of the light irradiated from the actual light source
device is as shown in FIG. 48. Taking into consideration the fact
that the energy of the lamp drops at the short wavelength region,
and further that the CCD spectral sensitivity properties lose
sensitivity in this region, the gain of the B2 band image is
excessively increased as a result of color adjustments processing
such as white balance and the like, thereby yielding an image with
a very great amount of noise.
[0189] Accordingly, with the present embodiment, the light quantity
for each band is adjusted at the light source side so that each
band image has appropriate SN properties even after performing
white balance taking into consideration the spectral properties
other than those of the filter, such as of the lamp, CCD, etc. Note
that the bandwidth restricting filter 92 has the spectral
properties shown in FIG. 44.
[0190] FIG. 49 illustrates the illumination timing for each band,
and the light quantity control timing at that time. With normal
observation wherein the bandwidth restricting filter 92 is not
inserted into the optical path, the electric power supply unit 10
receives control signals from the light adjusting circuit 43 at an
illumination timing indicated by a in FIG. 49 and controls the
voltage level of the driving voltage of the xenon lamp 11, and
performs light quantity control such as indicated by "b" in FIG.
49. The reason that the quantity of light is decreased during the
shielding period is to alleviate the heat generated from the
lamp.
[0191] On the other hand, on the narrow-band observation wherein
the bandwidth restricting filter 92 is inserted in the optical
path, the electric power supply unit 10 receives control signals
from the light adjusting circuit 43 at an illumination timing
indicated by "c" in FIG. 49 and controls the voltage level of the
driving voltage of the xenon lamp 11, and performs light quantity
control such as indicated by "d" in FIG. 49.
[0192] Thus, according to the present embodiment, in addition to
the advantages of the third embodiment, the spectral distributions
of light irradiated from the light source in the event that the
voltage level of the driving voltage of the xenon lamp 11 is not
controlled (see FIG. 48) become spectral properties such as shown
in FIG. 50, so light quantity control wherein each band image has
suitable SN properties can be realized.
[0193] FIG. 51 is a configuration diagram illustrating the
configuration of an endoscope device according to a fifth
embodiment of the present invention.
[0194] The fifth embodiment is almost the same as the third
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0195] As shown in FIG. 51, with the electronic endoscope 3
according to the present embodiment, a color chip 101 is disposed
at the front face of the CCD 2 to configure a color CCD 2a, thus
configuring the synchronous system type endoscope device 1. Color
image signals from the color CCD 2a are converted into color image
data at the A/D converter 24, subsequently subjected to color
separation at the color separating circuit 102, then input to the
white balance circuit 25, and stored in a memory 103, via the
selector 26, subsequently subjected to interpolation processing and
the like at the image processing circuit 30, following which
desired image processing is performed.
[0196] The light source device 4 comprises the bandwidth
restricting filter 92 having multi-peak band-pass properties (see
FIG. 38, FIG. 40, FIG. 44), and the bandwidth restricting filter 92
is arranged so as to be inserted to and extracted from the optical
path by the filter moving motor 87, based on control signals from
the mode switch-over circuit 42 which has received instructions
signals from the mode switch-over switch 41.
[0197] With the present embodiment thus configured, the bandwidth
restricting filter 92 is inserted into the optical path, whereby
the spectral properties of the image taken by the CCD 2 via the
color chip 101 become discrete narrow-band band images (see FIG.
39), and the narrow-band band images are subjected to image
processing, so the same advantages as those of the third embodiment
can be obtained with the present embodiment, as well.
[0198] FIG. 52 is a configuration diagram illustrating the
configuration of an endoscope device according to a sixth
embodiment of the present invention.
[0199] The sixth embodiment is almost the same as the fifth
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0200] With the present embodiment, as shown in FIG. 52, a light
source device 112 for narrow-band observation is provided
separately from a light source device 111 for normal
observation.
[0201] The light source device 111 has the xenon lamp 11 as
illumination light emitting means, and the white light from the
xenon lamp 11 passes through the diaphragm device 13 and is cast
into the incident face of the light guide 15 of the electronic
endoscope comprising the color CCD 2a.
[0202] Also, the light source device 112 has an extra-high pressure
mercury lamp 113 as the illumination light emitting means, wherein
the light from the extra-high pressure mercury lamp 113 is adjusted
at the diaphragm device 13, and is cast into an incident face of an
illumination probe 114, inserted into a treatment equipment channel
(not shown) of the electronic endoscope 3, via the bandwidth
restricting filter 92.
[0203] Now, the diaphragm device 13 for each of the light source
devices 111 and 112 are arranged so as to be controlled by the
light adjusting circuit 43 based on control signals from the mode
switch-over circuit 42 and light adjustment control parameters from
the light adjustment control parameter switch-over circuit 44.
[0204] With the present embodiment, at the time of normal
observation, the diaphragm device 13 of the light source device 111
is set on the bright side, while the diaphragm device 13 of the
light source device 112 is set on the dark side or is shielded.
[0205] Also, the time of narrow-band light observation, the
diaphragm device 13 of the light source device 112 is set on the
bright side, while the diaphragm device 13 of the light source
device 111 is set on the dark side or is shielded.
[0206] Setting each of the diaphragm devices 13 thus means that
narrow-band light is irradiated from the emitting face of the
illumination probe 114 at the time of narrow-band light
observation, so the same advantages as those of the fifth
embodiment can be obtained with the present embodiment, as
well.
[0207] Next, a seventh embodiment of the present invention will be
described with reference to FIG. 53 to FIG. 57.
[0208] FIG. 53 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 54 is a configuration
diagram illustrating the configuration of the light mixing unit
shown in FIG. 53, FIG. 55 is a diagram illustrating an example of
spectral distribution of the xenon lamp shown in FIG. 53, FIG. 56
is a diagram illustrating an example of spectral distribution of
the extra-high pressure mercury lamp shown in FIG. 53, and FIG. 57
is a diagram illustrating an example of spectral distribution of
light irradiated from the light source device at the time of
narrow-band observation with the light mixing unit shown in FIG.
54.
[0209] The seventh embodiment is almost the same as the third
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0210] As shown in FIG. 53, the light source device 3 according to
the present embodiment comprises the xenon lamp 11 having a
relatively broad spectral distribution as shown in FIG. 55, and the
extra-high pressure mercury lamp 113 with multiple emission line
spectrums such as shown in FIG. 56 that is provided on the optical
path, and further comprises a light mixing unit 121 for mixing the
light from the xenon lamp 11 and the extra-high pressure mercury
lamp 113. The light that is mixed at the light mixing unit 121 is
supplied to the electronic endoscope via the diaphragm device 13
and rotating filter 91.
[0211] As shown in FIG. 54, the light mixing unit 121 comprises a
diaphragm 122 for adjusting the light quantity of light from the
xenon lamp 11, a diaphragm 123 for adjusting the light quantity of
light from the extra-high pressure mercury lamp 113, a half mirror
124 for synthesizing the light coming through the diaphragm 122 and
diaphragm 123, and outputting onto the optical path of the
diaphragm device 13 and rotating filter 91, and a diaphragm control
circuit 125 for controlling the diaphragm 122 and the diaphragm 123
based on control signals from the mode switch-over circuit 42.
[0212] When performing narrow-band observation, the diaphragm 122
at the front face of the xenon lamp 11 is closed by the diaphragm
control circuit 125, and the diaphragm 123 at the front face of the
extra-high pressure mercury lamp 113 is opened, so that the
illumination light emitted from the light mixing unit has spectral
properties equivalent to those of the extra-high pressure mercury
lamp 113. This light is then transmitted through an R1G1B1 rotating
filter 91, consequently irradiating RGB narrow-band frame sequence
light such as shown in FIG. 57 into the living body tissue.
[0213] On the other hand, at the time of normal observation, the
diaphragm 122 at the front face of the extra-high pressure mercury
lamp 113 is closed by a diaphragm control circuit 125, and the
diaphragm 123 at the front face of the xenon lamp 11 is opened, so
that RGB frame sequence light with natural color reproduction is
irradiated on the living body tissue.
[0214] According to such an embodiment, the same advantages as
those of the third embodiment can be obtained.
[0215] Now, for obtaining intermediate illumination light between
the xenon lamp and the extra-high pressure mercury lamp 113,
adjusting the degree of opening of the diaphragms at the front face
of both the lamps mixes both lamp properties at a percentage
corresponding to the ratio of opening the diaphragms, thereby
yielding illumination light having spectral properties differing
from either of the lamps.
[0216] Also, the actions of the light adjusting circuit 43 are
changed by the light adjustment control parameters changing the
light adjusting table according to switching over of the mode, and
the change in the spectral distribution of the illumination light
compensates for the change in the quantity of illumination light.
Consequently, images which are constantly of a suitable brightness
can be observed even when switching over to illumination light
spectral distributions suiting such an object as observing the
surface structure of mucous membranes in detail.
[0217] FIG. 58 is a configuration diagram illustrating the
configuration of an endoscope device according to an eighth
embodiment of the present invention.
[0218] The eighth embodiment is almost the same as the first
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0219] As shown in FIG. 58, the present embodiment is a narrow-band
observation endoscope device having a narrow-band light source
device 131 dedicated for supplying narrow-band frame sequence light
to the electronic endoscope 3, and a narrow-band video processor
132 dedicated for processing the narrow-band frame sequence light
captured by the electronic endoscope 3
[0220] A narrow-band rotating filter 133 provided in the light
source device 131 is configured of the R2 filter 14r2, G2 filter
14g2, and B2 filter 14b2 (see FIG. 4), for generating narrow-band
RGB frame sequence light.
[0221] Thus, the present embodiment also enables narrow-band
observation with narrow-band frame sequence light.
[0222] Also, in the event that the narrow-band light source device
131 having the narrow-band rotating filter 133 is connected to the
narrow-band video processor 132, information relating to the type
of illumination light spectral properties of the narrow-band light
source device 131 are output from the control circuit 17 of the
narrow-band illumination light device 131 to the light adjustment
control parameter switch-over circuit 44, as identification
signals. The correlation between the identification signals and the
control parameters is recorded in the light adjustment parameter
switch-over circuit 44 beforehand in the form of a correlation
table, and appropriate control signals are output to the light
adjusting circuit 43 based on the correlation table, and
consequently, light adjustment control according to the
illumination light spectral properties is enabled.
[0223] FIG. 59 and FIG. 60 relate to a ninth embodiment of the
present invention, wherein FIG. 59 is a configuration diagram
illustrating the configuration of an endoscope device, and FIG. 60
is a diagram illustrating an adapter having a band restricting
filter which is mountable on the tip of the electronic endoscope
shown in FIG. 59.
[0224] The ninth embodiment is almost the same as the first
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0225] As shown in FIG. 59, the present embodiment comprises a
normal observation electronic endoscope 151, an endoscope device
154 having a light source device 152 for supplying normal
observation frame sequence light to the electronic endoscope 151
and a video processor 153 for performing signal processing on
image-pickup signals from the electronic endoscope 151, and a
narrow-band light observation endoscope device 155 provided
separately from this endoscope device 154. Here, this light source
device 152 has the xenon lamp 11 and diaphragm device 13, and the
rotating filter 91 upon which are disposed the R1 filter 14r1, G1
filter 14g1, and B1 filter 14b1.
[0226] The narrow-band light observation endoscope device 155
comprises a small-diameter electronic endoscope 156 to be inserted
through the treatment equipment channel of the electronic endoscope
151, a light source device 157 for supplying narrow-band frame
sequence light to the small-diameter electronic endoscope 156, and
a video processor 158 for signal processing image-pickup signals
from the small-diameter electronic endoscope 156. The light source
device 152 has the extra-high pressure mercury lamp 113 and
diaphragm device 13, and a rotating filter 160 upon which are
disposed the R2 filter 14r2, G2 filter 14g2, and B2 filter
14b2.
[0227] Normal observation is performed using the endoscope device
154, and narrow-band light observation is performed using the
narrow-band light observation endoscope device 155.
[0228] According to the present embodiment, the same advantages as
those of the first embodiment can be obtained.
[0229] Further, a normal endoscope can be connected to the
narrow-band light observation endoscope device 155.
[0230] Also, an adapter 171 having a bandwidth restricting filter
170 such as shown in FIG. 58 may be mounted on the tip of the
above-described electronic endoscope. Thus, narrow-band light
observation can be performed using the endoscope device 154.
[0231] Also, while FIG. 60 is an example of mounting the adapter
171 to which is applied the bandwidth restricting filter 170 on the
front face of the objective optical system 21, an arrangement may
be made wherein the bandwidth restricting filter 170 is mounted in
the front face of an illumination lens 172.
[0232] As described above, according to the above first through
ninth embodiments, tissue information of a desired depth near the
tissue surface of living body tissue can be obtained.
[0233] Next, a tenth embodiment of the present invention will be
described with reference to FIG. 61 through FIG. 74.
[0234] FIG. 61 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 62 is a configuration
diagram illustrating the configuration of the rotating filter shown
in FIG. 61, FIG. 63 is a diagram illustrating the spectral
properties of a first filter set of the rotating filter shown in
FIG. 62, FIG. 64 is a diagram illustrating the spectral properties
of a second filter set of the rotating filter shown in FIG. 62,
FIG. 65 is a diagram illustrating the structure of the living body
tissue to be observed with the endoscope device shown in FIG. 1, in
the layer direction, FIG. 66 is a diagram describing the state of
the illumination light from the endoscope device shown in FIG. 61
reaching the living body tissue in the layer direction, FIG. 67 is
a diagram illustrating each of the band images from frame sequence
light transmitted through the first filter set shown in FIG. 63,
FIG. 68 is a diagram illustrating each of the band images from
frame sequence light transmitted through the second filter set
shown in FIG. 64, FIG. 69 is a diagram describing light adjustment
control by a light adjusting circuit shown in FIG. 61, FIG. 70 is a
configuration diagram illustrating the configuration of the image
processing circuit shown in FIG. 61, FIG. 71 is a diagram
illustrating a color image of a narrow-band RGB image obtained by
the image processing circuit shown in FIG. 70, FIG. 72 is a diagram
describing the creation of a matrix such that an average color tone
is maintained in the 3.times.3 matrix circuit shown in FIG. 70,
FIG. 73 is a diagram illustrating an example of settings of the LUT
shown in FIG. 70, and FIG. 74 is a configuration diagram
illustrating the configuration of a modification made to the color
conversion processing circuit shown in FIG. 70.
[0235] As shown in FIG. 61, an endoscope device 201 according to
the present embodiment comprises an electronic endoscope 203 having
a CCD 202 serving as image-pickup means to be inserted into the
body cavity and capture images of tissue within the body cavity, a
light source device 204 for supplying illumination light to the
electronic endoscope, and a video processor 207 for performing
signal processing on image-pickup signals from the CCD 202 of the
electronic endoscope 203 and displaying endoscopic images on an
observation monitor 205 or encoding the endoscopic images and
outputting to an image filing device 206 as compressed images.
[0236] The light source device 204 is configured of a xenon lamp
211 for emitting illumination light, a heat ray cut filter 212 for
shielding heat rays from the white light, a diaphragm device 213
for controlling the light quantity of the white light through the
heat ray cut filter 212, a rotating filter 214 for turning the
illumination light into frame sequence light, a condenser lens 216
for collecting the frame sequence light coming through the rotating
filter 214 onto the incident face of a light guide 215 disposed
within the electronic endoscope 203, and a control circuit 217 for
controlling the rotation of the rotating filter 214.
[0237] As shown in FIG. 62, the rotating filter 214 is formed in a
disk-like shape and has a double structure with the center as the
rotating axis, wherein an R1 filter 214r1, a G1 filter 214g1, and a
B1 filter 214b1 making up a first filter set for outputting frame
sequence light having overlapping spectral properties suitable for
natural color reproduction such as indicated in FIG. 63 situated on
the outer sector, and wherein an R2 filter 214r2, a G2 filter
214g2, and a B2 filter 214b2 making up a second filter set for
outputting narrow-band frame sequence light having discrete
spectral properties enabling extraction of desired deep tissue
information such as indicated in FIG. 64 situated on the inner
sector. As shown in FIG. 61, the rotating filter 214 is rotated by
the control circuit 217 performing driving control of a rotating
filter motor 218, and movement in the radial direction (movement
which is perpendicular to the optical path of the rotating filter
214, which is selectively moving the first filter set or second
filter set of the rotating filter 214 onto the optical path) is
performed by a mode switch-over motor 219 by control signals from a
mode switch-over circuit 242 within the later-described video
processor 207.
[0238] Note that electric power is applied to the xenon lamp 211,
diaphragm device 213, rotating filter motor 218, and mode
switch-over motor 219, from an electric power supply unit 210.
[0239] Returning to FIG. 61, the video processor 207 is configured
comprising: a CCD driving circuit 220 for driving the CCD 202; an
amplifier 222 for amplifying image-pickup signals wherein images
are captured from the body cavity tissue by the CCD 202 through an
objective optical system 221; a process circuit 223 for performing
correlated double sampling and noise reduction and so forth, with
regard to image-pickup signals coming through the amplifier 222; an
A/D converter 224 for converting the image-pickup signals passing
through the process circuit 223 into image data of digital signals;
a white balance circuit 225 for subjecting the image data from the
A/D converter 224 to white balance processing; the selector 226 and
synchronizing memory 227a, 227b, and 227c, for synchronizing the
frame sequence light from the rotating filter 214; an image
processing circuit 230 for reading out each set of image data of
the frame sequence light stored in the synchronizing memory 227a,
227b, 227c, and subjecting these to gamma correction processing,
outline enhancement processing, color processing, etc; D/A circuits
231a, 231b, and 231c, for converting the image data from the image
processing circuit 230 into analog signals; an encoding circuit 234
for encoding the output of the D/A circuits 231a, 231b, and 231c;
and a timing generator 235 for inputting synchronizing signals
synchronized with the rotation of the rotating filter 214 from the
control circuit 217 of the light source device 204, and outputting
various types of timing signals to the above-described
circuits.
[0240] Also, a mode switch-over switch 241 is provided in the
electronic endoscope 203, with the output of this mode switch-over
switch 241 being output to the mode switch-over circuit 242 within
the video processor 207. The mode switch-over circuit 242 of the
video processor 207 outputs control signals to a light adjusting
circuit 243, a light adjustment control parameter switch-over
circuit 244, and mode switch-over motor 219 of the light source
device 204. The light adjustment control parameter switch-over
circuit 244 outputs light adjustment control parameters
corresponding to the first filter set or second filter set of the
rotating filter 214 to the light adjusting circuit 243, and the
light adjusting circuit 243 controls the diaphragm device 213 of
the light source device 204 based on the control signals from the
mode switch-over circuit 242 and light adjustment parameters from
the light adjustment control parameter switch-over circuit 244, so
as to perform appropriate brightness control.
[0241] As shown in FIG. 65, a body cavity tissue 251 often has a
structure wherein there is a distribution of different absorbent
material such as blood vessels in the depth direction, for example.
There is primarily a greater distribution of capillaries 252 near
the surface of mucus membranes, blood vessels 253 which are thicker
than the capillaries are also distributed along with capillaries at
the middle layer which is deeper than this layer, and even thicker
blood vessels 254 are distributed at even deeper layers.
[0242] On the other hand, the permeation depth of the light in the
depth direction as to the body cavity tissue 251 is dependent on
the wavelength of light, and with illumination light containing the
visible region, as shown in FIG. 66, in the case of light with a
short wavelength such as blue (B), the light only reaches around
the surface layer due to the absorption properties and scattering
properties at the living body tissue, being subjected to absorption
and scattering within the range up to that depth, so light coming
out from the surface is observed. Also, in the case of green (G)
light with a wavelength longer than that of blue (B) light, the
light reaches a depth deeper than the range where the blue (B)
light reaches, is subjected to absorption and scattering within the
range at that depth, and light coming out from the surface is
observed. Further, red (R) light with a wavelength longer than that
of green (G) light, reaches a range even deeper.
[0243] At the time of performing normal observation, the mode
switch-over circuit within the video processor 207 controls the
mode switch-over motor 219 with control signals, so that the R1
filter 214r1, G1 filter 214g1, and B1 filter 214b1, making up the
first filter set of the rotating filter 214, are positioned on the
optical path of the illumination light.
[0244] With the R1 filter 214r1, G1 filter 214g1, and B1 filter
214b, the wavelength regions are each overlapped as shown in FIG.
63, so at the time of normal observation of the body cavity tissue
251, a band image having shallow layer and middle layer tissue
information containing a great amount of tissue information at the
shallow layer such as shown by "a" in FIG. 67 is captured in the
image-pickup signals which are captured by the CCD 202 with the B1
filter 214b1, a band image having shallow layer and middle layer
tissue information containing a great amount of tissue information
at the middle layer such as shown in "b" in FIG. 67 is captured
into the image-pickup signals that are captured by the CCD 202 with
the G1 filter 214g1, and further, a band image having middle layer
and deep layer tissue information containing a great amount of
tissue information at the deep layer such shown in "c" in FIG. 67
is captured into the image-pickup signals which are captured by the
CCD 202 with the R1 filter 214r1.
[0245] These RGB image-pickup signals are synchronized with the
video processor 207 and subjected to signal processing, thus
enabling an endoscopic image with desired or natural color
reproduction to be obtained as an endoscopic image.
[0246] On the other hand, upon the mode switch-over switch 241 of
the electronic endoscope 203 being pressed, the signals thereof are
input into the mode switch-over circuit 242 of the video processor
207. The mode switch-over circuit 242 outputs control signals to
the mode switch-over motor 219 of the light source device 204,
thereby moving the first filter set of the rotating filter 214 that
was on the optical path at the time of normal observation, and
drives the rotating filter 214 with respect to the optical path so
that the second filter set is positioned upon the optical path.
[0247] In the event of performing narrow-band light observation of
the body cavity tissue 251 with the second filter set, the R2
filter 214r2, G2 filter 214g2, and B2 filter 214b2 make the
illumination light to be narrow-band frame sequence light with
discrete spectral properties as shown in FIG. 64, so a band image
having tissue information at a shallow layer such as shown in "a"
in FIG. 68 is captured into the image-pickup signals which are
captured by the CCD 202 with the B2 filter 214b2, a band image
having tissue information at the middle layer such as shown in "b"
in FIG. 68 is captured into the image-pickup signals which are
captured by the CCD 202 with the G2 filter 214g2, and a band image
having tissue information at the deep layer such as shown in "c" in
FIG. 68 is captured into the image-pickup signals which are
captured by the CCD 202 with the R2 filter 214r2.
[0248] As can be clearly understood from FIG. 63 and FIG. 64, at
this time, the quantity of transmitted light from the second filter
set is less than the quantity of transmitted light from the first
filter set, because the bands thereof are narrowed, so the light
adjusting circuit 243 controls the diaphragm device 213 by
outputting light adjustment control parameters according to the
first filter set or second filter set of the rotating filter 214,
from the light adjustment control parameter switch-over circuit 244
to the light adjusting circuit 243, thereby, as shown in FIG. 69,
controlling the diaphragm device 213 when making narrow-band light
observation so as to control light quantity Mx with a diaphragm
control curve 262 corresponding to a set value Lx, with respect to,
for example, a linear diaphragm control line 261 by the diaphragm
device 213 in normal observation, corresponding to the set value Lx
on an unshown setting panel of the video processor 207. Thus, image
data with sufficient brightness can be obtained at the time of
narrow-band light observation, as well.
[0249] Specifically, the aperture level value corresponding to the
light quantity setting value Lx changes from Mx1 to Mx2 as shown in
FIG. 69, being interlocked with changing the first filter set to
the second filter set, and consequently, the diaphragm is
controlled in the direction of being opened, and acts to compensate
for reduction in the quantity of illumination light by the filters
which narrows the band.
[0250] As shown in FIG. 70, an image processing circuit 230
comprises three sets each of LUTs 262a, 262b, 262c, 263a, 263b, and
263c, fore and aft, across a 3.times.3 matrix circuit 261, and a
coefficient changing circuit 264 for converting table data of the
LUTs 262a, 262b, 262c, 263a, 263b, and 263c, and the coefficients
of the 3.times.3 matrix circuit 261, thus configuring a color
conversion processing circuit 230a.
[0251] The RGB data input to the color conversion processing
circuit 230a is converted by the LUTs 262a, 262b, and 262c, for
each band data. Here, inverse .gamma. correction, non-linear
contrast conversion, etc., is performed.
[0252] Next, following color conversion being performed at the
3.times.3 matrix circuit 261, .gamma. correction and suitable tone
conversion processing is performed at the latter LUTs 263a, 263b,
and 263c.
[0253] Change can be made at a coefficient changing circuit 264 for
converting table data of the LUTs 262a, 262b, 262c, 263a, 263b, and
263c, and the coefficients of the 3.times.3 matrix circuit 261.
[0254] Changing with the coefficient changing circuit 264 is based
on control signals from the mode switch-over circuit 242 or a
processing conversion switch (not shown) provided on the operating
unit or the like of the electronic endoscope 203.
[0255] Upon receiving the control signals, the coefficient changing
circuit 264 calls up appropriate data from the coefficient data
described in the image processing circuit 230 beforehand, and
rewrites the current circuit coefficients with this data.
[0256] Next, the contents of color conversion processing will be
described specifically. Expression 1 shows an example of a color
conversion expression.
Expression 1
[0257] R.fwdarw.R
G.fwdarw..omega..sub.GG+.omega..sub.BB
B.fwdarw.B (1)
[0258] The processing according to Expression 1 is an example of
conversion for taking data generated by a B image having been mixed
with G at a certain ratio and taking this anew as a G image. Making
the illumination light for each band to be narrow-band can further
clarify that absorbents and scatterers such as blood vessel
networks differ according to depth position.
[0259] That is to say, the difference in information relating to
body structures which each band reflect can be further increased by
making the illumination light to be narrow-band.
[0260] In the event of observing these narrow-band RGB images as
color images, this will be an image such as shown in FIG. 71, for
example. The thick blood vessels are at deep positions, and are
reflected in the R band image, indicated by a blue color pattern as
the color thereof. The blood vessel network near the middle layers
is intensely reflected in the G image, and is indicated as a red
color pattern for the color image thereof. Of the blood vessel
networks, those existing near the surface of the mucous membrane
are represented as a yellow color pattern.
[0261] Particularly, the change in pattern near the surface of the
mucous membrane is crucial for early discovery and differential
diagnosis of early disorders. However, yellow patterns have little
contrast with the background mucous membrane, and accordingly the
visibility thereof tends to be low.
[0262] Accordingly, the conversion shown in Expression 1 is valid
for clearly reproducing the patterns near the surface of the mucous
membrane. Expression 1 can be expressed in matrix format as shown
in Expression 2.
Expression 2 ( R ' G ' B ' ) = ( 1 0 0 0 .omega. G .omega. B 0 0 1
) ( R G B ) ( 2 ) ##EQU00001##
[0263] Accordingly, adjusting the matrix coefficients through the
coefficient changing circuit 264 allows the user to adjust the
display effects. As for the operations, synchronously with a mode
switch-over switch (not shown) provided to the operating unit of
the electronic endoscope 203, the matrix coefficients are set to
default values from a through operation within the image processing
means.
[0264] The through operation here refers to a state wherein the
3.times.3 matrix circuit 261 carries a unit matrix, and the LUTs
262a, 262b, 262c, 263a, 263b, and 263c carry non-conversion tables.
Default values are to provide the matrix coefficients with set
values of, for example, .omega.G=0.2, .omega.B=0.8.
[0265] The user then operates a processing changing switch or the
like provided to the operating unit of the electronic endoscope 203
or the video processor casing panel or the like, and performs
adjustment so that the coefficients are .omega.G=0.4, .omega.B=0.6,
and so forth. If necessary, inverse .gamma. correction tables and
.gamma. correction tables are applied to the LUTs 262a, 262b, 262c,
263a, 263b, and 263c.
[0266] Next, description will be made wherein color correction is
performed so as to maintain an average color tone as much as
possible even in the event that the filter is switched, at the
color conversion processing circuit 230a.
[0267] As a result of filter switching, the spectral properties of
the illumination light change. Consequently, color reproduction
also changes. Depending on the state of usage or the user, there
may be cases wherein maintaining average color reproduction as much
as possible is desired while maintaining improved contrast of
minute structure at the surface of the mucous membrane. In such
cases, there is the need to change the operations by the
coefficient changing circuit 264 so as to perform color conversion
operations wherein the average color tone is maintained from the
through operation, in accordance with the filter switching.
[0268] Procedures for creating a matrix for maintaining average
color tone are shown below. As shown in FIG. 72, let us say that
the color distribution of a subject in an RGB color space moves
from a first distribution to a second distribution, corresponding
to filter switching. In such a case, at least three points are
selected from the first distribution (normally containing
distribution average and center-of-gravity data), and where in the
second distribution these three points move to is checked. Then, a
conversion matrix from the second distribution to the first
distribution is calculated using the three sets of data, and used
as the matrix coefficients for the 3.times.3 matrix circuit 261.
Note that three or more points can be selected and determined by
the method of least-squares.
[0269] Color reproduction which maintains average color tone as
much as possible can be attained even when switching filters, by
applying the above matrix coefficients to the LUTs 262a, 262b,
262c, 263a, 263b, and 263c, using inverse .gamma. correction and
.gamma. correction tables as necessary.
[0270] Also, image effects such as pigment dying can be reproduced
with a B image alone, taking advantage of the fact that the
narrow-band B image reflects the minute structures of the surface
of mucous membranes well, such as pit patterns. That is to say, the
output RGB data is configured of only the B data out of the RGB
data input by the matrix conversion expression indicated in
Expression 3.
Expression 3 ( R ' G ' B ' ) = ( 0 0 .omega. R 0 0 .omega. G 0 0
.omega. B ) ( R G B ) ( 3 ) ##EQU00002##
[0271] Adjusting the coefficients then allows effects such as
pigment dying images to be exhibited. For example, with settings
wherein .omega.B >>.omega.G, .omega.R, the image exhibits a
bluish tone, and has the tone of the same color as performing
indigo dying. Also, with settings wherein .omega.B, .omega.R
>>.omega.R, the image exhibits a purplish tone, and has the
tone of the same color as performing methyl violet dying. Further,
setting the LUT settings such as shown in FIG. 73 results in hard
reproduction for the contrast, and images with high contrast such
as with dyed images can be obtained.
[0272] Thus, according to the present embodiment, setting the
parameters of the color conversion processing circuit 230a
synchronously with the filter switching allows a representation
method which takes advantage of the characteristic of narrow-band
RGB illumination light, namely, permeation depth information, to be
realized, so tissue information at desired depths near the tissue
surface of living body tissue can be separated and visually
recognized.
[0273] Now, with the above embodiment, the color conversion
processing circuit 230a is described as a configuration with the
3.times.3 matrix circuit 261 at the center, but the same advantages
can be obtained by replacing the color conversion processing
circuit 230a with 3-dimensional LUTs 271 corresponding to each
band, as shown in FIG. 74. In this case, the coefficient changing
circuit 264 performs operations for changing the contents of the
tables based on control signals from the mode switch-over circuit
242.
[0274] Next, an eleventh embodiment of the present invention will
be described with reference to FIG. 75 through FIG. 78.
[0275] FIG. 75 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 76 is a configuration
diagram illustrating the configuration of the image processing
circuit shown in FIG. 75, FIG. 77 is a configuration diagram
illustrating the configuration of the color adjusting circuit shown
in FIG. 75, and FIG. 78 is a diagram illustrating the concept of
hue and saturation on a L*a*b* color space in the color adjusting
circuit shown in FIG. 75.
[0276] The eleventh embodiment is almost the same as the tenth
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0277] With the present embodiment, a case including means for
converting coordinates between a color space such as XYZ which is
not dependent on a device such as a monitor, and a color space such
as RGB which is dependent on a device, is shown as color conversion
of a color conversion processing circuit for changing operations
synchronously with operations of filter switching.
[0278] As shown in FIG. 75, a processing switch-over instructing
switch 281 is provided in the electronic endoscope 203, with the
image processing circuit 230 receiving control signals from the
mode switch-over circuit 242 and instruction signals from the
processing switch-over instructing switch 281, and performing the
later-described color conversion processing.
[0279] As shown in FIG. 76, a color conversion processing circuit
230b configured in the image processing circuit 230 comprises LUTs
282a, 282b, and 282c, which are set for each band, a 3.times.3
matrix circuit 283, a color adjusting circuit 284, a subsequent
stage 3.times.3 matrix circuit 285, subsequent LUTs 286a, 286b, and
286c, which are set for each band, and the coefficient changing
circuit 264.
[0280] RGB data which is first input to the preliminary LUTs 282a,
282b, and 282c is subjected to inverse .gamma. correction. This is
to cancel non-linear .gamma. correction which is performed taking
into consideration the .gamma. properties of the display device
such as a CRT, before color conversion processing.
[0281] Next, conversion is made at the preliminary 3.times.3 matrix
circuit 283, from RGB to XYZ which is a color space that is not
device-dependent. The conversion expression is shown in Expression
4.
[0282] In Expression 4, xi, yi, and zi (i=R, G, B) are xy
chromaticity coordinates of the primitive colors of the display
device such as a CRT or the like.
Expression 4 ( X Y Z ) = ( x R y r x G y G x B y B 1 1 1 z R y R z
G y G z B y B ) ( R G B ) ( 4 ) ##EQU00003##
[0283] Next, following being subjected to later-described
appropriate color adjustment at the color adjusting circuit 284,
conversion is made into device-dependent color space R'G'B' again
at the subsequent stage 3.times.3 matrix circuit 285 by Expression
5, and following .gamma. correction for monitor display at the
subsequent LUTs, output is made to the observation monitor 205.
Expression 5 ( R ' G ' B ' ) = ( x R y r x G y G x B y B 1 1 1 z R
y R z G y G z B y B ) - 1 ( ( X ) ' ( Y ) ' ( Z ) ' ) ( 5 )
##EQU00004##
[0284] Next, the operations of the color adjusting circuit 284 will
be described. As shown in FIG. 77, the color adjusting circuit 284
comprises a sensory color space conversion unit 287 which performs
conversion from XYZ to a sensory color space such as L*a*b*, a hue
and saturation conversion adjusting unit 288 which performs
conversion to hue and saturation which humans perceive to be the
three attributes of color, adjusts these values and performs
intuitive color adjustment, and then performs inverse conversion to
L*a*b*, and a sensory color inverse conversion unit 289 for
performing conversion to XYZ again.
[0285] Expression 6 shows the conversion expression between L*a*b*
and XYZ, and further, Expression 7 shows the conversion expression
from L*a*b* to hue Hab and Cab. Here, X.sub.w, Y.sub.w, and Z.sub.w
represent the XYZ values for reference white.
Expression 6 L * = 116 ( Y Y w ) 1 3 - 16 a * = 500 [ ( X X w ) 1 3
- ( Y Y w ) 1 3 ] b * = 200 [ ( X X w ) 1 3 - ( Z Z w ) 1 3 ] ( 6 )
Expression 7 C ab = a * 2 + b * 2 H ab = arctan ( b * a * ) ( 7 )
##EQU00005##
[0286] Also, FIG. 78 illustrates the concepts of hue and saturation
in a L*a*b* color space.
[0287] Once converted into hue and saturation, color adjustment can
be performed intuitively. For example, if a brighter color tone is
desired, this can be achieved by multiplying or adding the
saturation with a constant coefficient. Also, in the event that
change of the color toward blue or toward red is desired, the hue
value can be adjusted. Thus, intuitive color adjustment can be
realized at the color adjusting means.
[0288] Next, operations interlocked with the mode switch-over
circuit 242 and the processing switch-over instructing switch 281
will be described. A characteristic of observation with narrow-band
RGB illustration light is that, in the event that there are
different structures in the depth direction of the body, such as
blood vessel structures, these are represented with different
colors. Even more effective display can be made by enhancing the
saturation and rotating the hue as suitable in order to enhance
these characteristics even more.
[0289] Accordingly, being interlocked with the mode switch-over
circuit 242, the coefficient changing circuit 264 changes the
coefficients of the related circuit based on instruction signals
from the processing switch-over instructing switch 281, so that
through passage is allowed without color adjustment when performing
normal observation for example, and color adjustment is made for
narrow-band observation. Further, in the event of observation with
narrow-band RGB illumination light, the degree of enhancement of
saturation and the degree of rotation of hue is switched over
according to user preferences, the type of subject, etc., by
instructions of the processing switch-over instructing switch
281.
[0290] Also, the conversion from RGB to XYZ has been performed with
an expression based on a normal CRT device model, but may be
changed to the one as shown in Expression 8 with regard to a
calculation method of the luminance Y, of XYZ.
[0291] In Expression 8, change has been made such that the RGB
ratio can be specified at the time of calculating Y.
Expression 8 ( X Y Z ) = ( x R y r x G y G x B y B .omega. R
.omega. G .omega. B z R y R z G y G z B y B ) ( R G B ) ( 8 )
##EQU00006##
[0292] The B image of narrow-band RGB has a characteristic of
minute structures of the body mucous membrane surface being
reflected with high contrast. In order to reflect this information
in the luminance information, the weight .omega.B of B is increased
at the time of calculating Y. Generally, the luminance of B is low
as compared to RG (G is the greatest for human luminance
sensitivity), so calculating using Expression 6 with no change does
not reflect the information of B very much. Accordingly, it is
meaningful to adjust the weight of B as described above.
[0293] Each of the band images reflect different body structures
with narrow-band RGB images, so the weight can be adjusted with
Expression 8 according to objects of use. It is sufficient that
multiple types of weight combinations be prepared beforehand, so as
to be switched over under control of the processing switch-over
switch. Incidentally, Expression 7 is used for inverse conversion
from XYZ to RGB in this case.
[0294] Thus, with the present embodiment, as with the tenth
embodiment, a representation method which takes advantage of the
characteristic of permeation depth information of narrow-band RGB
illumination light can be realized by setting the parameters of the
color converting processing circuit 230a synchronously with the
filter switching, and accordingly, tissue information at desired
depths near the tissue surface of living body tissue can be
separated and visually recognized.
[0295] Next, a twelfth embodiment of the present invention will be
described with reference to FIG. 79 through FIG. 84.
[0296] FIG. 79 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 80 is a configuration
diagram illustrating the configuration of the rotating filter shown
in FIG. 79, FIG. 81 is a diagram illustrating the spectral
transmission properties of the filters G2, B2a, and B2b, of the
rotating filter shown in FIG. 80, FIG. 82 is a configuration
diagram illustrating the configuration of the band selecting
circuit shown in FIG. 79, FIG. 83 is a configuration diagram
illustrating the configuration of a modification made on the
rotating filter shown in FIG. 79, and FIG. 84 is a diagram
illustrating spectral transmission properties of the rotating
filter shown in FIG. 83.
[0297] The twelfth embodiment is almost the same as the tenth
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0298] As shown in FIG. 79, the present embodiment comprises four
pieces of synchronizing memory 227a, 227b, 227c, and 227d, for the
output of a selector 226, the image processing circuit 230 which
performs image processing with regard to the output of the four
pieces of synchronizing memories 227a, 227b, 227c, and 227d, D/A
circuits 231a, 231b, 231c, and 231d, which convert the four sets of
data processed by the image processing circuit 230 into analog
data, and a band selecting circuit for subjecting the output of the
D/A circuits 231a, 231b, 231c, and 231d to matrix computation and
outputting as three bands of data.
[0299] The reason that there are four sets of synchronizing memory
is that the second filter set of the double-structure rotating
filter 214 is configured of filters with four bandwidths, R2, G2,
B2a, and B2b as shown in FIG. 80, and the spectral transmittance
properties of these filters R2, G2, B2a, and B2b are as shown in
FIG. 81.
[0300] In the event that the rotating filter 214 is specified to
the second filter set (R2, G2, B2a, and B2b) by control signals of
the mode switch-over circuit 242 by control signals from the mode
switch-over instructing switch 241, the four band images are input
to the four pieces of synchronizing memories 227a, 227b, 227c, and
227d. The four band images are subjected to processing such as
color adjustment and the like at the image processing circuit 230,
then subjected to D/A conversion at the D/A circuits 231a, 231b,
231c, and 231d, and then input to a band selecting circuit 301.
[0301] The user uses a band switch-over instructing switch 302
provided on the operating unit of the electronic endoscope 203 to
specify which band of the four bands will be used to output an
image to the observation monitor 205.
[0302] As shown in FIG. 82, the band selecting circuit 301 is
configured of a 4.times.3 matrix circuit 305 and a matrix
coefficient changing circuit 306, wherein band switch-over
instructing signals output from the band switch-over instructing
switch 302 are input to the matrix coefficient changing circuit 306
provided to the band selecting circuit 301. The matrix coefficient
changing circuit 306 applies predetermined matrix coefficients to
the 4.times.3 matrix circuit 305, based on the band switch-over
instructing signals.
[0303] Expression 9 shows a matrix circuit expression.
Expression 9 ( d r d g d b ) = ( w 11 w 12 w 13 w 14 w 21 w 22 w 23
w 24 w 31 w 32 w 33 w 34 ) ( D R 2 D G 2 D B 2 a D B 2 b ) ( 9 )
##EQU00007##
[0304] As shown in FIG. 9, at the band selecting circuit 301, the
4.times.3 matrix coefficients act upon the input values for the
four band images (DR2, DG2, DB2a, and DB2b) to yield three output
signals (dr, dg, and db), and these signals are output to the
observation monitor 205 as trichromatic signals.
[0305] Expression 10 illustrates an example of matrix
coefficients.
Expression 10 M 1 = ( 1 0 0 0 0 1 0 0 0 0 1 0 ) M 2 = ( 1 0 0 0 0 1
0 0 0 0 0 1 ) M 3 = ( 0 0 1 0 0 0 1 0 0 0 0 1 ) M 4 = ( 0 0 1 0 0 0
1 0 0 0 1 0 ) M 5 = ( 1 0 0 0 0 1 0 0 0 0 0.2 0.8 ) ( 10 )
##EQU00008##
[0306] The coefficients set in M1 configure an image of R2, G2, and
B2a, while M2 is settings using B2b instead of B2a. Switching
between M1 and M2 can be made by, for example, setting B2a at a
center wavelength of near-ultraviolet light, and setting B2b to a
hemoglobin absorbing wavelength band (e.g., 415 nm), thereby
enabling using these as depending on conditions, as a mode for
observing minute irregularities near the surface of the mucous
membranes such as pit patterns in detail in the event that M1 is
applied, and a mode for observing in detail minute capillary
networks near the surface of the mucous membranes in the event that
M2 is applied.
[0307] Also, the coefficient M3, because the image is configured of
the two bands of B2a and B2b, is suitable for catching change in
scattering properties such as change in the cell structure near the
surface of the mucous membranes and the like, by configuring a
narrow-band filter with B2a and B2b in close approximation near 380
nm.
[0308] Also, in the event that simple observation of a single-color
image of a certain band as a monochrome image is desired, the
settings may be made as with M4, or the coefficients may be set as
in M5 to mix and output multiple bands at a certain ratio so as to
take advantage of the properties of each band.
[0309] Thus, according to the present embodiment, in addition to
the advantages of the tenth embodiment, there are no markedly dark
portions on the screen at the time of changing filters to switch
over from normal observation to narrow-band filter observation, and
light quantity sufficient to fully enable observation can be
obtained. Further, which band to use for image observation can be
selected from the multiple filters, so optimal observation images
according to the state of usage can be obtained.
[0310] Also, though the present embodiment describes the rotating
filter 214 as being a double structure, the rotating filter can be
made a single structure in the event that changing the B filter is
sufficient for obtaining image effects, thus configuring a rotating
filter 214 made up of four filters, as shown in FIG. 83. As for the
filter properties, there is a configuration wherein, for example,
only the B filter is made narrow-band, as shown in FIG. 84. The
object of this is to take advantage of the fact that the permeation
depth of light around this wavelength band to the body is shallow,
thereby improving contrast of body structures such as blood vessels
near the surface by the filter which narrows the band. Due to such
a configuration for the rotating filter 214, the user can obtain
optimal observation images by simply instructing band switching
over according to the state of observation, without switching
filters.
[0311] As described above, according to the tenth embodiment
through twelfth embodiment, tissue information at a desired depth
near the tissue surface of the living body tissue can be separated
and visually recognized.
[0312] Next, a thirteenth embodiment of the present invention will
be described with reference to FIG. 85 through FIG. 94.
[0313] FIG. 85 is a configuration diagram illustrating the
configuration of an endoscope device according to the present
invention, FIG. 86 is a configuration diagram illustrating the
configuration of the rotating filter shown in FIG. 85, FIG. 87 is a
diagram illustrating the spectral properties of the first filter
set of the rotating filter shown in FIG. 86, FIG. 88 is a diagram
illustrating the spectral properties of the second filter set of
the rotating filter shown in FIG. 86, FIG. 89 is a diagram
illustrating the structure of the living body tissue in the layer
direction to be observed with the endoscope device shown in FIG.
85, FIG. 90 is a diagram describing the state of the illumination
light from the endoscope device shown in FIG. 85 reaching the
living body tissue in the layer direction, FIG. 91 is a diagram
illustrating each of the band images from frame sequence light
transmitted through the first filter set shown in FIG. 87, FIG. 92
is a diagram illustrating each of the band images from frame
sequence light transmitted through the second filter set shown in
FIG. 88, FIG. 93 is a diagram describing light adjustment control
performed by a light adjusting circuit shown in FIG. 85, and FIG.
94 is a configuration diagram illustrating the configuration of the
image processing circuit shown in FIG. 85.
[0314] The thirteenth embodiment is almost the same as the tenth
embodiment, so only the differing points will be described, and the
same configurations will be denoted with the same reference
numerals and description thereof will be omitted.
[0315] As shown in FIG. 85, the endoscope device 401 according to
the present embodiment is configured of an electronic endoscope 403
which is inserted inside the body cavity and which has a CCD 402
serving as image-pickup means for capturing images of tissue within
the body cavity, a light source device 404 for supplying
illumination light to the electronic endoscope 403, and a video
processor 407 for subjecting image-pickup signals from the CCD 402
of the electronic endoscope 403 to signal processing and displaying
endoscopic images on an observation monitor 405 or encoding the
endoscopic images and outputting to an image filing device 406 as
compressed images.
[0316] The light source device 404 is configured of a xenon lamp
411 for emitting illumination light, a heat ray cut filter 412 for
shielding heat rays from the white light, a diaphragm device 413
for controlling the light quantity of the white light through the
heat ray cut filter 412, a rotating filter 414 for turning the
illumination light into frame sequence light, a condenser lens 416
for collecting the frame sequence light coming through the rotating
filter 414 onto the incident face of a light guide 415 disposed
within the electronic endoscope 403, and a control circuit 417 for
controlling the rotation of the rotating filter 414.
[0317] As shown in FIG. 86, the rotating filter 414 is formed in a
disk-like shape and has a double structure with the center as the
rotating axis, wherein an R1 filter 414r1, a G1 filter 414g1, and a
B1 filter 414b1 making up a first filter set for outputting frame
sequence light having overlapped spectral properties suitable for
natural color reproduction such as indicated in FIG. 87 are
situated on the outer sector, and wherein an R2 filter 414r2, a G2
filter 414g2, and a B2 filter 414b2 making up a second filter set
for outputting narrow-band frame sequence light having discrete
spectral properties enabling extraction of desired deep tissue
information such as indicated in FIG. 88 are situated on the inner
sector. As shown in FIG. 85, the rotating filter 414 is rotated by
the control circuit 417 performing driving control of the rotating
filter motor 418, and movement in the radial direction (movement
which is perpendicular to the optical path of the rotating filter
414, which is selectively moving the first filter set or second
filter set of the rotating filter 414 onto the optical path) is
performed by the mode switch-over motor 19 by control signals from
the mode switch-over circuit 442 within the later-described video
processor 417.
[0318] Note that electric power is applied to the xenon lamp 411,
diaphragm device 413, rotating filter motor 418, and mode
switch-over motor 419, from the electric power supply unit 410.
[0319] Returning to FIG. 85, the video processor 407 is configured
comprising a CCD driving circuit 420 for driving the CCD 402, an
amplifier 422 for amplifying image-pickup signals by which images
are captured of the body cavity tissue via the CCD 402 through the
objective optical system 421, a process circuit 423 for performing
correlated double sampling and noise reduction and so forth, with
regard to image-pickup signals coming through the amplifier 422, an
A/D converter 424 for converting the image-pickup signals passing
through the process circuit 423 into image data of digital signals,
a white balance circuit 425 for subjecting the image data from the
A/D converter 424 to white balance processing, a selector 426 and
synchronizing memories 427a, 427b, and 427c, for synchronizing the
frame sequence light from the rotating filter 414, an image
processing circuit 430 for reading out each set of image data of
the frame sequence light stored in the synchronizing memories 427a,
427b, 427c, and subjecting these to gamma correction processing,
outline enhancement processing, color processing, etc., D/A
circuits 431a, 431b, and 431c, for converting the image data from
the image processing circuit 430 into analog signals, an encoding
circuit 434 encoding the output of the D/A circuits 431a, 431b, and
431c, and a timing generator 435 for inputting synchronizing
signals synchronized with the rotation of the rotating filter 414
from the control circuit 417 of the light source device 404, and
outputting various types of timing signals to the above-described
circuits.
[0320] Also, a mode switch-over switch 441 is provided in the
electronic endoscope 403, with the output of this switch-over
switch 441 being output to a mode switch-over circuit 442 within
the video processor 407. The mode switch-over circuit 442 of the
video processor 407 outputs control signals to a light adjusting
circuit 443, a light adjustment control parameter switch-over
circuit 444, and mode switch-over motor 419 of the light source
404. The light adjustment control parameter switch-over circuit 444
outputs light adjustment control parameters corresponding to the
first filter set or second filter set of the rotating filter 414 to
the light adjusting circuit 443, and the light adjusting circuit
443 controls the diaphragm device 413 of the light source device
404 based on the control signals from the mode switch-over circuit
442 and light adjusting parameters from the light adjustment
control parameter switch-over circuit 444, so as to perform
appropriate brightness control.
[0321] As shown in FIG. 89, body cavity tissue 451 often has a
structure wherein there is a distribution of different absorbent
material such as blood vessels in the depth direction, for example.
A great number of capillaries 452 are mainly distributed near the
surface of mucus membranes, blood vessels 453 which are thicker
than the capillaries are also distributed along with capillaries at
the middle layer which is deeper than this layer, and even thicker
blood vessels 454 are distributed at even deeper layers.
[0322] On the other hand, the permeation depth of the light in the
depth direction as to the body cavity tissue 451 is dependent on
the wavelength of light, and with illumination light containing the
visible region, as shown in FIG. 90, in the case of light with a
short wavelength such as blue (B), the light only reaches around
the surface layer due to the absorption properties and scattering
properties at the living body tissue, being subjected to absorption
and scattering within the range up to that depth, and light coming
out from the surface is observed. Also, in the case of green (G)
light with a wavelength longer than that of blue (B) light, the
light reaches a depth deeper than the range where the blue (B)
light reaches, is subjected to absorption and scattering within the
range at that depth, and light coming out from the surface is
observed. Further, red (R) light with a wavelength longer than that
of green (G) light, reaches a range even deeper.
[0323] At the time of performing normal observation, the mode
switch-over motor 419 is controlled by the mode switch-over circuit
within the video processor 407 with control signals, so that the R1
filter 414r1, G1 filter 414g1, and B1 filter 414b1, making up the
first filter set of the rotating filter 414, are positioned on the
optical path of the illumination light.
[0324] With the R1 filter 414r1, G1 filter 414g1, and B1 filter
414b, the wavelength regions are each overlapped as shown in FIG.
87, so at the time of normal observation of the body cavity tissue
451, a band image having shallow layer and middle layer tissue
information containing a great amount of tissue information at the
shallow layer such shown in "a" in FIG. 91 is captured in the
image-pickup signals taken by the CCD 402 with the B1 filter 414b1,
a band image having shallow layer and middle layer tissue
information containing a great amount of tissue information at the
middle layer such as shown in "b" in FIG. 91 is captured in the
image-pickup signals taken by the CCD 402 with the G1 filter 414g1,
and further, a band image having middle layer and deep layer tissue
information containing a great amount of tissue information at the
deep layer such shown in "c" in FIG. 91 is captured in the
image-pickup signals taken by the CCD 402 with the R1 filter
414r1.
[0325] These RGB image-pickup signals are synchronized with the
video processor 407 and subjected to signal processing, thus
enabling an endoscopic image with desired or natural color
reproduction to be obtained as an endoscopic image.
[0326] On the other hand, upon the mode switch-over switch 441 of
the electronic endoscope 403 being pressed, the signals thereof are
input to the mode switch-over circuit 442 of the video processor
407. The mode switch-over circuit 442 outputs control signals to
the mode switch-over motor 419 of the light source device 404,
thereby moving the first filter set of the rotating filter 414 that
was on the optical path at the time of normal observation, and
drives the rotating filter 414 with regard to the optical path so
that the second filter set is positioned upon the optical path.
[0327] In the event of performing narrow-band light observation of
the body cavity tissue 451 with the second filter set, the R2
filter 414r2, G2 filter 414g2, and B2 filter 414b2 make the
illumination light to be narrow-band frame sequence light with
discrete spectral properties as shown in FIG. 88, so a band image
having tissue information at a shallow layer such as shown in "a"
in FIG. 92 is captured in the image-pickup signals taken by the CCD
402 with the B2 filter 414b2, a band image having tissue
information at the middle layer such as shown in "b" in FIG. 92 is
captured in the image-pickup signals taken by the CCD 402 with the
G2 filter 414g2, and a band image having tissue information at the
deep layer such as shown in "c" in FIG. 92 is captured in the
image-pickup signals taken by the CCD 402 with the R2 filter
414r2.
[0328] As can be clearly understood from FIG. 87 and FIG. 88, at
this time, the quantity of transmitted light from the second filter
set is less than the quantity of transmitted light from the first
filter set, since the bands thereof are narrowed, so the light
adjusting circuit 443 controls the diaphragm device 413 by the
light adjustment control parameter switch-over circuit 444
outputting light adjustment control parameters according to the
first filter set or second filter set of the rotating filter 414 to
the light adjusting circuit 443, thereby, as shown in FIG. 93,
controlling the diaphragm device 413 when making narrow-band light
observation so as to control light quantity Mx with a diaphragm
control curve 462 corresponding to a set value Lx, as to, for
example, a linear diaphragm control line 461 by the diaphragm
device 413 in normal observation, corresponding to the set value Lx
on an unshown setting panel of the video processor 407.
[0329] Specifically, the aperture level value corresponding to the
light quantity setting value Lx changes from Mx1 to Mx2 as shown in
FIG. 93, in a manner synchronous with changing the first filter set
to the second filter set, and consequently, the diaphragm is
controlled in the direction of being opened, and acts to compensate
for reduction in the quantity of illumination light by narrowing
the bands of the filters.
[0330] The image processing circuit 430 of the present embodiment
has a processing structure for calculating IHb (hemoglobin index)
which is a value correlated with the hemoglobin concentration in
blood, using two of the band image information from RGB, and
specifically, as shown in FIG. 94, RGB signals input to the image
processing circuit 430 are subjected to inverse .gamma. correction
processing for removing the .gamma. correction performed for CRT
display at the inverse .gamma. correction processing unit 461, with
table conversion or the like.
[0331] Next, with regard to the GB signals subjected to inverse
.gamma. correction, signals to be sent to the subsequent processing
are selected based on control signals from the mode switch-over
circuit 442 with the selector unit 462. Next, following tone
inversion processing at a tone inversion processing unit 463,
multiplication with an R signal is performed at the multiplier 464.
Finally, after being subjected to logarithmic transformation at a
logarithmic transformation unit 465, output is made from the image
processing circuit 430.
[0332] As for the output format from the image processing circuit
430, pseudo color images may be generated based on the IHb, or one
band image, e.g., the R image may be substituted for the IHb
image.
[0333] With conventional IHb, an expression of 32.times.Log 2 (R/G)
is being used. This expression takes advantage of the fact that the
G band image reflects intensely blood information.
[0334] On the other hand, narrow-banding of the filter reflects
intensely surface capillaries to the B image. Accordingly, the B
and G images following filter switching differ in depth where the
blood vessels exist, so B reflects information of the surface
layer, and G reflects layer positions deeper than that.
[0335] Accordingly, with the present embodiment, upon the mode
switch-over switch 441 being pressed and the mode entering the
narrow-band observation mode, the IHb value (32.times.Log 2 (R/B))
of the surface layer of the mucous membrane based on B information,
and the IHb value (32.times.Log 2 (R/G)) of the middle layer of the
mucous membrane based on G information can be switched between and
used by switching over the operations of the selector unit 462
shown in FIG. 94, so tissue information at a desired depth near the
tissue surface of the living body tissue can be separated and
visually recognized.
[0336] Now, while the operations of the selector unit 462 have been
described as being based on control signals from the mode
switch-over circuit 442, a separate switch may be provided on the
operating unit or the like of the electronic endoscope 403.
[0337] Next, a fourteenth embodiment of the present invention will
be described with reference to FIG. 95 through FIG. 99.
[0338] FIG. 95 is a configuration diagram illustrating the
configuration of an endoscope device, FIG. 96 is a configuration
diagram illustrating the configuration of the image processing
circuit shown in FIG. 95, FIG. 97 is a configuration diagram
illustrating the configuration of the filtering execution unit
shown in FIG. 96, FIG. 98 is a diagram illustrating the filter
frequency properties of the filtering execution unit shown in FIG.
97, and FIG. 99 is a diagram illustrating RGB images taken when in
the narrow-band observation mode in FIG. 95.
[0339] The fourteenth embodiment is almost the same as the
thirteenth embodiment, so only the differing points will be
described, and the same configurations will be denoted with the
same reference numerals and description thereof will be
omitted.
[0340] The present embodiment relates to an endoscope which is
capable of switching the spectral properties of illumination light
to narrow-band RGB properties, and which has, being interlocked
therewith, functions for changing light quantity control parameters
such as light adjustment tables, and for changing image processing
parameters.
[0341] As shown in FIG. 95, a processing switch-over instructing
switch 470 is provided for the electronic endoscope 403, and the
image processing circuit 430 receives control signals form the mode
switch-over circuit 442 and instruction signals from the processing
switch-over instructing switch 470, and performs the
later-described color conversion processing.
[0342] Conventionally, spatial frequency filters such as FIR
filters have been used for image quality improvement and image
enhancement processing in endoscopic image processing, and have
been effective in assisting in observation.
[0343] The image processing circuit 430 according to the present
embodiment is of a configuration wherein this spatial frequency
filtering is applied to narrow-band RGB images, and as shown in
FIG. 96, is configured of a filtering execution unit 471 for
performing spatial frequency filtering processing with regard to
input RGB images, a data converting unit 472 for performing
conversion of the output results of the filtering execution unit
471 such as adjusting each of RGB to within an 8-bit level, and a
coefficient converting unit 473 for changing the operations of the
filtering execution unit based on control signals from the filter
switch-over circuit 442 and instruction signals from the processing
switch-over instructing switch 470.
[0344] As shown in FIG. 97, the filtering execution unit 471 is
made up of filtering units 481, 482, and 483, which perform
5.times.5 mask computation with regard to each of the RGB image
data, and adders 484, 485, and 486 which perform weighting on the
output of the filtering units 481, 482, and 483 and add to each of
the RGB image data, wherein the coefficient changing unit 473 sets
mask coefficients to the filtering units 481, 482, and 483 and
weight coefficients to the adders 484, 485, and 486.
[0345] Accordingly, by performing computation such as shown in
Expression 11, wherein the image data is represented by R(x, y),
G(x, y), B(x, y), the output of the filtering units 481, 482, and
483 by Rs(x, y), Gs(x, y), Bs(x, y), and the weight coefficients by
.omega.R, .omega.G, and .omega.B, spatial frequency filtering
processing results R'(x, y), G'(x, y), and B'(x, y) with the filter
frequency properties such as shown in FIG. 98 for example, are
output.
Expression 11
[0346] R'(x,y)=R(x,y)+.omega.RRs(x,y)
G'(x,y)=G(x,y)+.omega.GGs(x,y) B'(x,y)=B(x,y)+.omega.BBs(x,y)
(11)
[0347] The filter properties shown in FIG. 98 are properties which,
while suppressing enhancement of noise components as much as
possible in the order of M1, M2, and M3, enhance the high-frequency
components, and the enhanced bands are shifted to high frequencies
in order. Such filters with different enhanced bands are each
individually applied to respective bands.
[0348] That is to say, as shown in FIG. 99, upon the mode
switch-over switch 441 being pressed to enter the narrow-band
observation mode, the B image has smaller blood vessel patterns
than the R image, i.e., higher frequency properties, and M3 is
applied rather than filter M1 in order to reproduce these patterns
more clearly. The R image is contrary, and application of M1 is
more suitable than M3. Thus, it is important to use the filter
properties according to the contents of the body information which
the bands reproduce.
[0349] Also, such filter properties are effective for narrow-band
RGB images, and separate filter properties are required for normal
observation. Accordingly, the coefficient changing unit 473 changes
the filter properties to those which are optimal according to the
mode switch-over circuit 442. Control by instruction signals from
the processing switch-over instructing switch 470 performs
adjustment of enhancement level and so forth, for example.
[0350] Thus, according to the present embodiment as well, tissue
information at a desired depth near the tissue surface of the
living body tissue can be separated and visually recognized.
[0351] Next, a fifteenth embodiment of the present invention will
be described with reference to FIG. 100 through FIG. 103.
[0352] FIG. 100 is a configuration diagram illustrating the
configuration of an image processing circuit, FIG. 101 is a diagram
illustrating a tone correction table in the pre-processing unit in
FIG. 100, FIG. 102 is a diagram illustrating histogram distribution
applied to edge extracting processing in the edge extracting
processing unit shown in FIG. 100, and FIG. 103 is a diagram
describing processing in the pattern extracting unit shown in FIG.
100.
[0353] The fifteenth embodiment is almost the same as the
fourteenth embodiment, so only the differing points will be
described, and the same configurations will be denoted with the
same reference numerals and description thereof will be
omitted.
[0354] The present embodiment illustrates a configuration which
changes parameters for extracting angiography patterns or
extracting minute structure patterns on mucous membrane surfaces in
interlocking with filter switching. Narrow-band RGB images are
characterized in that the independency of information represented
between bands is high. For example, in the narrow-band observation
mode wherein the mode switch-over switch 441 is pressed,
differential information is reflected between bands, such as shown
in FIG. 99, wherein the B image reflects minute structure patterns
on mucous membrane surfaces and blood vessel networks near the
surface layer of mucous membranes, the G image reflects blood
vessel networks existing near the middle layers, and the R image
reflects relatively thicker blood vessel networks existing at deep
layers of the mucous membranes, and each type of information is
deeply related with the change of the living body tissue in the
depth direction. With regard to such narrow-band RGB images, more
effective results can be expected by further optimizing the
parameters rather than applying pattern extraction processing in
normal observation.
[0355] Accordingly, as shown in FIG. 100, the image processing
circuit 430 according to the present embodiment comprises a band
selector unit 491 for selecting each of the RGB band image data,
which selects a band to apply to the processing in the subsequent
pattern extracting processing unit 492, which comprises
pre-processing unit 493, edge extracting processing unit 494, and
pattern extracting unit 495.
[0356] Here, one band or multiple bands may be used, and selection
is made according to extracted information. In the event that
extraction of patterns of minute structures at the surface of
mucous membranes is desired, the B image is selected here. Or, in
the event that the position of thick blood vessels in layers of the
mucous membranes is desired, the R image is selected.
[0357] In the pattern extracting processing unit 492,
pre-processing is performed at the pre-processing unit 493. In
general pre-processing, suitable pre-processing is performed
according to subsequent processing, such as distortion correction,
tone correction, and so forth. In the event of performing
processing such as for angiography patterns, distortion correction
processing for correcting distortion aberration of the image-pickup
optical system, and histogram smoothing processing for
standardizing concentration distribution is performed. For example,
in the case of tone correction, a tone correction table F such as
shown in FIG. 101 is applied to band data f(x, y) input to the
pre-processing unit 493, to obtain output g(x, y) (=F (f(x, y)).
Note that in the tone correction table in FIG. 101, curve b
converts to a stronger contrast than curve a.
[0358] Next, in the edge extracting processing unit 494, edge
extraction processing is performed. A method wherein a trough in a
histogram distribution is discovered and binarization processing is
performed at that level as shown in FIG. 102, or a method wherein
edge extraction is performed using a differential operator, can be
used for this.
[0359] Next, at the pattern extracting unit 495, assuming the area
of the region A as M for example, as shown in FIG. 103, this M is
compared with a predetermined threshold value .theta., and in the
event that M<.theta., the region A is removed as an unnecessary
pattern, and only patterns having regions of blood vessels and the
like having area of .theta. or greater are extracted. Specifically,
elimination and consolidation of patterns is performed by expansion
or reduction processing, or collation with reference patterns.
[0360] With the series of processing performed at the pattern
extracting processing unit 492, parameters must be optimized for
each piece of information represented in each band. For example, in
the pattern extracting unit 495, in the event that extracting blood
vessels running at deep portions from the R image is desired,
operations are made to eliminate fine independent points as much as
possible, and in the event of extracting capillary angiography
patterns from the B image, operations are made to leave the fine
patterns as much as possible.
[0361] The processing results of the pattern extracting processing
unit 492 are output to a final stage image synthesizing unit 496,
and at the image synthesizing unit 496, image synthesizing for
reflecting the pattern extracting results in the image is
performed. Here, processing for adding the pattern extracting
results to the original RGB image, or processing for configuring a
monochromatic image from pattern extraction results alone, is
performed.
[0362] The operations of the above-described image processing
circuit 430 optimize the overall operations by the coefficient
changing unit 473 changing the coefficients of the processing units
based on control signals from the mode switch-over circuit 442 and
processing switch-over instructing switch 470. With regard to the
mode switch-over circuit 442, control is made so as to bypass
pattern extracting processing in the case of normal RGB
illumination, and pattern extraction processing based on control
signals from the processing switch-over instructing switch 470 is
performed in the image processing circuit 430 in the event of
narrow-band RGB illumination.
[0363] Thus, according to the present embodiment as well, tissue
information at a desired depth near the tissue surface of the
living body tissue can be separated and visually recognized.
[0364] Embodiments of the present invention have thus been
described, but it is needless to say that the present invention is
by no means restricted to the above embodiments, and various
modifications may be made within the spirit and scope of the
present invention.
INDUSTRIAL APPLICABILITY
[0365] As described above, according to the present invention,
firstly, an endoscope device and light source device capable of
obtaining tissue information of a desired depth near the tissue
surface of the living body tissue, can be provided.
[0366] Also, secondly, an endoscope device whereby tissue
information of a desired depth near the tissue surface of the
living body tissue can be separated and visually recognized, can be
provided.
* * * * *