U.S. patent application number 11/370977 was filed with the patent office on 2006-07-27 for confocal probe and endoscope device.
This patent application is currently assigned to PENTAX Corporation. Invention is credited to Rogerio Jun Mizumo.
Application Number | 20060167344 11/370977 |
Document ID | / |
Family ID | 32599234 |
Filed Date | 2006-07-27 |
United States Patent
Application |
20060167344 |
Kind Code |
A1 |
Mizumo; Rogerio Jun |
July 27, 2006 |
Confocal probe and endoscope device
Abstract
A confocal probe unit is provided with a scanning type confocal
probe, which includes at least one scanning mirror, and a
transparent substrate on which the at least one scanning mirror is
mounted. The transparent substrate is inserted in an optical path
of the confocal probe such that a light beam proceeding along the
optical path is deflected by the scanning mirror.
Inventors: |
Mizumo; Rogerio Jun;
(Saitama-ken, JP) |
Correspondence
Address: |
GREENBLUM & BERNSTEIN, P.L.C.
1950 ROLAND CLARKE PLACE
RESTON
VA
20191
US
|
Assignee: |
PENTAX Corporation
Tokyo
JP
|
Family ID: |
32599234 |
Appl. No.: |
11/370977 |
Filed: |
March 9, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10699699 |
Nov 4, 2003 |
|
|
|
11370977 |
Mar 9, 2006 |
|
|
|
Current U.S.
Class: |
600/168 ;
600/160; 600/173 |
Current CPC
Class: |
A61B 1/063 20130101;
A61B 5/0068 20130101; A61B 1/00172 20130101; A61B 1/00096 20130101;
A61B 5/0084 20130101; A61B 1/00009 20130101 |
Class at
Publication: |
600/168 ;
600/160; 600/173 |
International
Class: |
A61B 1/06 20060101
A61B001/06 |
Foreign Application Data
Date |
Code |
Application Number |
Nov 5, 2002 |
JP |
2002-321322 |
Nov 5, 2002 |
JP |
2002-321323 |
Claims
1. A confocal endoscope, comprising: a surface observing system
which allows an observation, via said objective lens, of a surface
of in-vivo tissues inside a human cavity at a first magnification;
and a confocal observing system which allows at least one of an
observation, via said objective lens, of a surface image and a
tomogram at a second magnification which is greater than the first
magnification.
2. The confocal endoscope according to claim 1, wherein said
surface observing system and said confocal observing system have a
common objective optical system.
3. The confocal endoscope according to claim 2, wherein an optical
axis of said surface observing system and an optical axis of said
confocal observing system substantially coincide with each other at
least in said common objective optical system.
4. The confocal endoscope according to claim 1, wherein said
confocal observing system includes: an objective optical system; a
scanning system that scans at least one of the surface and a
section of the in-vivo tissues to receive light reflected thereat;
and a pickup system that selectively transmits the light reflected
by the in-vivo tissues on a focal plane of an objective optical
system using a pin hole.
5. An endoscope device, comprising: a first light source that emits
light that illuminates an object to be observed; a second light
source that emits a light beam to be scanned to illuminate the
object; a surface observing system that allows an observation, via
said objective lens, of a surface of in-vivo tissues inside a human
cavity at a first magnification; and a confocal observing system
that scans the light beam emitted by said second light source, said
confocal observing system allowing an observation, via said
objective lens, of at least one of a surface image and a tomogram
at a second magnification which is greater than the first
magnification.
Description
[0001] This is a divisional application of U.S. patent application
Ser. No. 10/699,699 filed Nov. 4, 2003, the contents of which are
expressly incorporated by reference herein in its entirety.
BACKGROUND OF THE INVENTION
[0002] The present invention relates to a confocal probe to be
employed in an endoscope device and a confocal endoscope device for
observing tissues inside the human body and the like.
[0003] Conventionally, when tissues of a human body are examined,
parts of the tissues are cut using a treatment tool such as a
forceps for cutting. Then, the cut parts of the tissues are
examined. Such an examination requires a relatively long time, and
it has been difficult to apply medical treatment quickly.
[0004] Recently, a confocal optical scanning probe for non-invasive
imaging has been known. Typically, the confocal probe is configured
to illuminate tissues inside a human body with a scanning laser
beam, and receives a reflected beam that is reflected at a focal
point of an objective optical system of the confocal probe.
Examples of such a confocal probe are disclosed in Japanese Patent
No. 3032720 and No. 3052150.
[0005] The confocal probe is configured such that a pin hole is
provided, in front of a detector, at a position conjugate with an
object-side focal point of the objective optical system. With this
configuration, the detector only receives the reflected light,
which is reflected by the tissues, at a point on which the light is
focused. The detector, which is connected to an image processing
unit, receives the reflected light passed through the pin hole, and
performs photoelectric transformation.
[0006] In order to capture two-dimensional or three-dimensional
images of the tissues, the laser beam is scanned on the tissues.
For this purpose, the confocal probe is provided with scanning
mirrors for scanning the laser beam along two-dimensional
directions, or along three-dimensional directions.
[0007] Each of the scanning mirrors employed in the confocal probe
is formed on semi-conductive material such as a silicon substrate.
In a conventional confocal probe, the silicon substrate mounting
the scanning mirror is typically secured inside a device with
supporting members secured on an inner wall of a main body of the
device.
[0008] As above, the supporting members are located on an outer
side of the scanning mirror (i.e., apart from the optical axis of
the probe), in which case, the diameter of the probe tends to be
larger. Further, in conventional confocal probes, a plurality of
mirrors for scanning a beam in different directions are formed on
different silicon substrates. Therefore, the manufacturing process
of the scanning mirrors and assembling process thereof tends to be
complicated, which may increase manufacturing costs.
[0009] The scanning optical system is generally made of glass
material such as BK7 or quart glass. The CTE (coefficient of
thermal expansion) of the silicon substrate is several ten of times
as much as the CTE of the BK7 or quart glass. Therefore, when a
relatively large thermal change occurs, a positional relationship
of the optical system and the scanning mirrors is shifted, which
causes the optical path of the scanning laser beam to be displaced.
Due to this relatively worse thermal characteristic of the probe,
under a relatively high temperature around the probe, it is
difficult to keep a precise location of the image.
SUMMARY OF THE INVENTION
[0010] The present invention is advantageous in that a relatively
small diameter of a confocal probe can be realized, manufacturing
and assembling process can be simplified, and a confocal probe
having excellent thermal characteristics can be provided.
[0011] According to an aspect of the invention, there is provided a
scanning type confocal probe, which is provided with at least one
scanning mirror, and a transparent substrate on which the at least
one scanning mirror is mounted. The transparent substrate is
inserted in an optical path of the confocal probe such that a light
beam passing along the optical path is deflected by the at least
one scanning mirror.
[0012] Optionally, the scanning type confocal probe includes a
first scanning mirror that deflects the light beam in a first
predetermined direction, and a second scanning mirror that deflects
the light beam in a second predetermined direction which is
perpendicular to the first predetermined direction. In a particular
case, the first scanning mirror and the second scanning mirror may
be mounted on the same transparent substrate.
[0013] Alternatively, the scanning type confocal probe includes a
scanning mirror that deflects the light beam in a first
predetermined direction and in a second predetermined direction
which is perpendicular to the first predetermined direction, and a
fixed mirror. In this case, the scanning mirror and the fixed
mirror may be mounted on the same transparent substrate.
[0014] Further optionally, the probe may include an objective lens,
and the objective lens and the transparent substrate are made of
the same optical material.
[0015] Still optionally, the scanning type confocal probe may be
provided with a pin hole that allows light reflected by in-vivo
tissues on an object side focal plane of the objective lens to pass
through and shields light reflected by the tissues on portions
other than the object side focal plane of the objective lens.
[0016] In a particular case, the scanning type confocal probe
includes a single mode optical fiber that receives and transmits
light from the tissues via the objective lens, in which an object
lens side end surface of the optical fiber functions as the pin
hole.
[0017] According to another aspect of the invention, there is
provided a confocal endoscope, which includes a surface observing
system which allows an observation, via the objective lens, of a
surface of in-vivo tissues inside a human cavity at a first
magnification, and a confocal observing system which allows an
observation, via the objective lens, of a surface image and/or
tomogram at a second magnification which is greater than the first
magnification.
[0018] Optionally, the surface observing system and the confocal
observing system have a common objective optical system.
[0019] Further, an optical axis of the surface observing system and
an optical axis of the confocal observing system substantially
coincide with each other at least in the common objective optical
system.
[0020] In a particular example, the confocal observing system
includes an objective optical system, a scanning system that scans
the surface and/or section of the tissues to receive light
reflected thereat, and a pickup system that selectively transmits
the light reflected by the tissues on a focal plane of an objective
optical system using a pin hole.
[0021] According to a further aspect of the invention, there is
provided an endoscope device, which is provided with a light source
that emits a light beam for illuminating an object to be observed,
a scanning type confocal probe which includes at least one scanning
mirror and a transparent substrate on which the at least one
scanning mirror is mounted, the transparent substrate being
inserted in an optical path of the confocal probe such that a light
beam passing along the optical path is deflected by the at least
one scanning mirror, and an image reproducing system that
reproduces an image of the object using light reflected by the
object and passed through the confocal probe.
[0022] In a particular case, the endoscope device may include a
first scanning mirror that deflects the light beam in a first
predetermined direction, and a second scanning mirror that deflects
the light beam in a second predetermined direction which is
perpendicular to the first predetermined direction. It should be
noted that the first scanning mirror and the second scanning mirror
may be mounted on the same transparent substrate.
[0023] In another case, the endoscope device may include a scanning
mirror that deflects the light beam in a first predetermined
direction and in a second predetermined direction which is
perpendicular to the first predetermined direction, and a fixed
mirror. Also in this case, the scanning mirror and the fixed mirror
may be mounted on the same transparent substrate.
[0024] Optionally, the endoscope device may include an objective
lens, and the objective lens and the transparent substrate are made
of the same optical material.
[0025] According to another aspect of the invention, there is
provided an endoscope device, which is provided with a first light
source that emits light for illuminating an object to be observed,
a second light source that emits a light beam to be scanned to
illuminate the object, a surface observing system which allows an
observation, via the objective lens, of a surface of in-vivo
tissues inside a human cavity at a first magnification, and a
confocal observing system which scans the light beam emitted by the
second light source, the confocal observing system allowing an
observation, via the objective lens, of a surface image and/or
tomogram at a second magnification which is greater than the first
magnification.
BRIEF DESCRIPTION OF THE ACCOMPANYING DRAWINGS
[0026] FIG. 1 is a block diagram of a scanning type confocal probe
according to a first embodiment of the invention;
[0027] FIG. 2 is a perspective view of a micromirror employed in
the confocal probe in each embodiment;
[0028] FIG. 3 is a block diagram of a scanning type confocal probe
according to a second embodiment of the invention;
[0029] FIG. 4 is a block diagram of a scanning type confocal probe
according to a third embodiment of the invention; and
[0030] FIG. 5 is a block diagram of a scanning type confocal
endoscope according to a fourth embodiment of the invention.
DESCRIPTION OF THE EMBODIMENTS
[0031] Hereinafter, referring to the accompanying drawings,
scanning type confocal probes according to embodiments of the
invention will be described.
[0032] FIG. 1 shows a block diagram of a scanning type confocal
probe device 500 according to a first embodiment of the invention.
The confocal probe device 500 includes a scanning type confocal
probe unit 100, a processing unit 300 and a monitor 400.
[0033] The confocal probe unit 100 is inserted in a forceps channel
of an endoscope (not shown), which is inserted in a human cavity.
An image inside the human cavity (e.g., tissues) can be captured
using the probe unit 100. The captured image is processed by the
processing unit 300 and is displayed on the monitor 400.
[0034] As shown in FIG. 1, the processing unit 300 includes a laser
source 310, a coupler 320, a light receiving element 330, a CPU
(Central Processing Unit) 340, an image processing circuit 350 and
an operation panel 360.
[0035] The laser source 310 according to the first embodiment emits
an He--Ne laser having a wavelength of 421 nm. It is known that the
shorter the wavelength of the laser beam is, the higher the
resolution of the image is. It should be noted that the laser
source 310 is not limited to one that emits the He--Ne laser, and
may be one that emits Ar+ laser (488 nm).
[0036] The laser beam emitted by the laser source 310 is introduced
to the confocal probe unit 100 through the coupler 320.
[0037] The confocal probe unit 100 includes, as shown in FIG. 1, an
optical fiber 110, a GRIN (Gradual Index) lens 120, a glass
substrate 130, micromirrors 140 and 150, and an objective lens
170.
[0038] The optical fiber 110 is a single mode fiber, and transmits
the laser beam emitted by the processing unit 300 to the GRIN lens
120.
[0039] The GRIN lens 120 is a lens that is configured such that the
refractive index thereof gradually changes therein. It is known
that the GRIN lens enables downsizing of an optical system. The
laser beam passed through the optical fiber 110 is incident on the
GRIN lens 120, which collimates the laser beam. The collimated
laser beam is directed toward the glass substrate 130.
[0040] The micromirrors 140 and 150 are mounted on the glass
substrate 130. Specifically, the glass substrate 130 has a first
surface 130a on which the micromirror 140 is mounted, and a second
surface 130b on which the micromirror 150 is mounted. The first
surface 130a and the second surface 130b are parallel with each
other. The glass substrate 130 is made of glass material such as
BK7 or quart glass, which is generally used for optical elements.
The glass substrate 130 is arranged such that the first surface
130a and the second surface 130b incline with respect to an optical
axis of the probe unit 100 by 45 degrees, and the laser beam
emitted from the GRIN lens 120 is reflected by the micromirror 140,
then reflected by the micromirror 150 and is incident on the
objective lens 170. It should be noted that the inclination angle
(45 degrees) of the first and second surfaces 130a and 130b with
respect to the optical axis described above is an example, and can
be changed depending on various conditions such as an refractive
index of the glass substrate 130 and a space inside the probe unit
100.
[0041] FIG. 2 is a perspective view of the micromirror 140. Since
the micromirror 150 has the same structure of the micromirror 140,
only the micromirror 140 will be described. The micromirror 140
includes a plate member 161, torsion bars 162 and a supporting
frame 163, which are formed integrally by etching a silicon plate.
The plate member 161 is provided with a mirror section 164 which is
formed, for example, by evaporating reflective material (e.g.,
aluminum, gold or dielectric-multilayer). Further, on an upper
surface of the micromirror 140 (i.e., on upper surfaces of the
plate member 161, torsion bars 162 and the supporting frame 163), a
planar coil 165 formed of a thin copper layer is provided. A pair
of yoke units 166, each having a permanent magnet and a yoke, are
arranged to extend in a longitudinal direction of the torsion bars
162.
[0042] The yoke units 166 generate a magnetic field in a direction
substantially parallel with the plate member 161 and substantially
perpendicular to the longitudinal direction of the torsion bars 162
(i.e., in X' direction in FIG. 2). When an electrical current is
supplied to the planar coil 165, driving forces (torque) that are
parallel with the Z' direction and opposite to each other are
generated at sides of the plate member 161 extending in Y'
direction in accordance with Fleming's left hand law. The quantity
of the torque is substantially proportional to the electrical
current supplied to the planar coil 165.
[0043] In accordance with the generated torque, the plate member
161 rocks in a direction indicated by arrow A in FIG. 2. Since the
plate member 161 and the torsion bars 162 are formed integrally, as
the plate member 161 rotates, the torsion bars 162 are twisted,
which generates elastically reactive force. With this mechanism,
the plate member 161 rotates until the torque and the reactive
force balance. When the plate member 161 is located at a position
where the torque and the reactive force balance, the plate member
161 stops rotating and stays the balance position.
[0044] The micromirror 140 and the micromirror 150 are mounted on
the glass substrate 130 such that torsion bars 162 of the
micromirror 140 and the torsion bars 162 of the micromirror 150 are
oriented orthogonally to each other. When the plate member 161 of
the micromirror 140 rotates, the laser beam scans in an X-direction
(see FIG. 1). When the plate member 161 of the micromirror 150
rotates, the laser beam scans in the Y-direction (see FIG. 1). As
shown in FIG. 1, the X direction and Y direction are perpendicular
to the optical axis of the probe unit 100, and are parallel with a
surface 10 to be examined.
[0045] Although not shown, each of the micromirrors 140 and 150 has
a pair of detection coils on an opposite side of the surface of the
plate member 161 formed with the planar coil 165. The electrical
current supplied to the planar coil 165 includes a driving current
for rotating the plate member 161, and an AC current for detecting
the displacement angle (i.e., a rotation angle) of the plate member
161. As the AC current flows through the planar coil 165, due to
mutual inductance between the planar coil 165 and the detection
coils, induced voltages are generated across each detection
coil.
[0046] If the pair of detection coils are arranged at the same
distance with respect to the planar coil 165 at opposite sides,
when the plate member 161 is in its neutral state (no torque is
generated), a difference of the induced voltages is zero. When an
electrical current is supplied and the plate member 161 rotates,
one of the pair of coils becomes closer to the planar coil 165,
while the other becomes apart from the planar coil 165. Therefore,
a difference occurs between the voltages induced in the pair of
detection coils. By detecting the difference of the induced
voltages, the displaced angle (i.e., the rotation angle) of the
micromirror can be detected.
[0047] The collimated laser beam directed toward the micromirror
140 emerges from the first surface 130a, is reflected by the
micromirror 140 and is incident on the first surface 130a. The
laser beam proceeds toward the micromirror 150. That is, the laser
beam emerges from the second surface 130b, is reflected by the
micromirror 150, and is incident on the second surface 130b again.
The laser beam then emerges from the first surface 130a and is
directed to the objective lens 170.
[0048] The objective lens is formed of glass material similar to
the glass substrate 130 (e.g., BK7 or quart glass). The collimated
laser beam emerged from the first surface 130a is converged on the
surface or at a certain depth of the target portion 10 to be
examined.
[0049] The light beam incident on the target portion 10 is
reflected thereat, the reflected light being incident on the
objective lens 170. If the light is reflected at the focal point of
the objective lens 170, the light reflected by the target area and
entered the objective lens 170 is collimated by the objective lens
170. Then, the light returns the path along which the emerging beam
proceeded to the target portion 10. The reflected light is then
incident on the GRIN lens 120.
[0050] As described above, the optical fiber 110 is the single mode
fiber. Therefore, the diameter of the core is very small, ranging
from 3 to 9 .mu.m (which varies depending on the working
wavelength). An end surface 110a of the optical fiber 110 is
located at a position which is conjugate with the focal point on
the object side of the objective lens 170. Thus, among the light
flux incident on the target portion 10, those converged on the
target portion 10 is converged by the GRIN lens 120 on the end
surface 110a of the optical fiber 110. The light flux converged on
the end surface 110a is transmitted through the core of the optical
fiber 110, and received by the light receiving element 330 through
the coupler.
[0051] The reflected light that is reflected on surfaces of the
target portion 10 other than the focal plane of the objective lens
170 is not converged on the end surface 110a, and thus does not
enter the core of the optical fiber 110. Accordingly, such light is
not transmitted to the processing unit 300. That is, the optical
fiber 110 transmits only the light reflected by the target plane 10
on the focal plane of the objective lens 170 to the processing unit
300. Thus, the end surface 110a of the optical fiber 110 functions
as a pin hole which shields the light reflected by surfaces other
than the focal plane of the objective lens 170, and functions to
allow the image obtained by the optical system provided to the
confocal probe unit 100 to the processing unit 300.
[0052] Further, an aperture stop (i.e., a pin hole) is provided on
a focal plane of the GRIN lens 120, and the optical system inside
the probe unit 100 is a telecentric optical system, which has
little loss of light amount.
[0053] The light beam received by the light receiving element 330
is converted into electrical signals corresponding to the received
light amount (i.e., image signals), which is transmitted to the
image processing circuit 350. The image processing circuit applies
predetermined image processing and generates video signals such as
a composite video signal, an RGB signal, or an S-video signal. The
video signal is applied to the monitor 400, thereby an image of the
target portion 10 on the focal plane of the objective lens 170,
which image is captured by the probe unit 100, is displayed.
[0054] By operating the operation panel 360 of the processing unit
300, an operator can selectively observe the images captured by the
confocal probe unit 100.
[0055] Specifically, when the operator operates the operation panel
360, signals corresponding to the operation are transmitted to the
CPU 340. Then, the CPU 340 drives the micromirror 140 and the
micromirror 150 so that the laser beam scans the target portion 10
in the X direction and the Y direction. The reflected light on the
focal plane of the objective lens 170 is transmitted to the
processing unit 300 as described above.
[0056] It should be noted that, by varying a moving (scanning)
range of the micromirror 140 and/or micromirror 150, a field of
view of an observing image can be varied with ease. That is, when
the scanning range is smaller, an image in a small observing field
is obtained, while when the scanning range is larger, an image
within a wide area can be obtained.
[0057] FIG. 3 is a block diagram showing a confocal probe device
500y according to a second embodiment of the invention. In FIG. 3,
the elements identical to those shown in FIG. 1 are given the same
reference numerals, and description thereof will not be
repeated.
[0058] The confocal probe device 500y includes a confocal probe
unit 100y, the processing unit 300 and the monitor 400.
[0059] According to the confocal probe device 500y, only one
micromirror is used to obtain a two-dimensional image of the
tissues. In the confocal probe device 500y, a two-axis scanning
type (which is capable of deflecting the laser beam both in the X
direction and in the Y direction) micromirror 150y is employed
instead of the second micromirror 150 of the first embodiment.
Further, the first micromirror 140 of the first embodiment is
replaced with a mirror (e.g., a single metal layer or multilayer
coating of dielectric substance) 140y.
[0060] It should be noted that, in the structure shown in FIG. 3,
the mirror 140y is formed on the first surface 130a and the
micromirror 150y is mounted on the second surface 130b. This can be
reversed, that is, the mirror may be formed on the second surface
130b and the two-axis scanning type micromirror may be mounted on
the first surface 130a.
[0061] FIG. 4 is a block diagram showing a confocal probe device
500z according to a third embodiment of the invention. In FIG. 4,
the elements identical to those shown in FIG. 1 are given the same
reference numerals, and description thereof will not be
repeated.
[0062] As shown in FIG. 4, the confocal probe device 500z includes
a confocal probe unit 100z, a processing unit 300z and the monitor
400.
[0063] The processing unit 300z includes a laser source 310z,
having a Brewster window, through which polarized beam is emitted.
The beam emerged from the Brewster window is an S-polarized beam
with respect to a polarization layer 181, which will be described
later.
[0064] The laser beam emitted by the laser source 310Z is incident
on the optical fiber 110 of the confocal probe unit 100z through
the coupler 320. The light beam transmitted through the optical
fiber 110 is collimated by the GRIN lens 120 and is introduced to a
polarization beam splitting cube 180.
[0065] The polarization beam splitting cube 180 has a polarization
layer 181, which is arranged to form an angle of 45 degrees with
respect to the optical axis of the probe unit 100z. The
polarization layer 181 reflects the S-polarization beam and
transmits the P-polarization beam.
[0066] On surfaces of the polarization beam splitting cube 180
perpendicular to the optical axis of the probe unit 100z, .lamda./4
plate 190 and .lamda./4 plate 191 are formed, respectively. The
.lamda./4 plates function to convert linear polarization light into
circular polarization light, and convert the circular polarization
light into the linear polarization light.
[0067] The S-polarization beam emitted by the laser source 310z is
directed to the GRIN lens 120 through the coupler 320 and the
optical fiber 110. The GRIN lens 120 collimates the incident beam.
The collimated S-polarized beam is incident on the polarization
layer 181, and reflected thereby to proceed toward the .lamda./4
plate 190. The beam passes the .lamda./4 plate, thereby the
S-polarization beam being converted into the circular polarization
beam and incident on the micromirror 140.
[0068] The beam is then reflected by the micromirror 140 and passes
through the .lamda./4 plate 190 again, thereby the circular
polarization beam being converted into a P-polarized beam. Since
the polarization layer 181 allows the P-polarization beam to pass
therethrough, the beam reflected by the micromirror 140 and passed
through the .lamda./4 plate 190 passes through the polarization
layer 181 and incident on the .lamda./4 plate 191. The beam is
converted into the circular polarization beam and is reflected by
the micromirror 150. The reflected beam passes through the
.lamda./4 plate 191 again, thereby it is converted to the
S-polarization beam and incident on the polarization layer 181.
Since the beam is the S-polarization beam, it is reflected by the
polarization layer 181, and is directed to the objective lens 170
as shown in FIG. 4. The beam, which is a collimated beam, is
converged by the objective lens 170 on the target portion 10 on the
surface thereof or at a predetermined depth.
[0069] The beam reflected on the target portion 10 returns the same
path as described above, and enters the GRIN lens 120. Similarly to
the first embodiment, only the light reflected on the focal plane
of the objective lens 170 is transmitted to the processing unit
300z. The reflected light is received by the light receiving
element 330, which generates an image signal. The image signal is
then processed in the image processing circuit 350 and a focused
image is displayed on the monitor 400.
[0070] It should be noted that, according to the third embodiment,
even if a position of the polarization beam splitting cube 180 with
respect to the probe unit 100z is varied, the optical axis of the
GRIN lens 120 and the optical axis of the objective lens 170 are
maintained to coincide with each other. Therefore, accurate imaging
can be ensured.
[0071] Similar to the second embodiment, one of the micromirrors
140 and 150 of FIG. 4 can be replaced with a two-axis type
micromirror and the other can be replaced with a mirror.
[0072] FIG. 5 is a block diagram showing a confocal endoscope
device 1500 according to a fourth embodiment of the invention. The
confocal endoscope device 1500 includes a confocal endoscope 1100,
a processing unit 1300 and the monitor 400.
[0073] The confocal endoscope 1100 includes a surface observing
section for observing inside the human cavity with a relatively
wide field of view. The surface observing section includes an
objective lens 1110, a CCD (Charge Coupled Device) 1120, a light
guide 1130 and a projection lens 1131.
[0074] According to the embodiment, a color image is obtained in
accordance with a frame sequential method. The processing unit 1300
has an RGB rotatable filter unit 1331, which is inserted in an
optical path of a light source 1330. The RGB filter unit 1331 has
filters of R (red), G (green) and B (blue). The RGB filter unit
1331 is rotated to locate the RGB filters sequentially in the
optical path. The light passed through the RGB filter unit 1331 is
converged by a converging lens 1332, transmitted through the light
guide 1130, and directed to the target portion 10 through the
projection lens 1131. With this configuration, the target portion
10 is illuminated with the light passed through RGB filters,
sequentially.
[0075] The CCD 1120 captures an image of the target portion 10
illuminated with RGB light via the objective lens 1110, and a
polarization unit 1150, sequentially to obtain images of respective
color components, which are combined to generate a color image by
the processing unit 1300.
[0076] The CCD 1120 outputs image signals corresponding to the
captured images of the target portion 10. The image signals are
transmitted to a pre-processing circuit 1310 of the processing unit
1300. The pre-processing circuit 1310 amplifies the received image
signals and applies a sampling/holding process. The image signals
are then transmitted to an A/D (analog to digital) converter
1311.
[0077] The A/D converter 1311 converts the received image signals
(which are analog signals) to digital signals. The digital signals
are divided by the endoscope image signal processing circuit 1312,
in synchronism with switching of the RGB filter unit 1331, into R
component signal, G component signal, and B component signal, which
are stored in an RGB memory 1313.
[0078] The RGB memory 1313 has three frame memories for the RGB
components, and stores the separated color image signals in the
respective frame memories. The thus stored image signals are
readout simultaneously, converted into analog signals by a D/A
converter 1314, and transmitted to an endoscope video signal output
circuit 1315.
[0079] The endoscope video signal output circuit 1315 converts the
transmitted analog signal into an RGB video signal, a composite
video signal or an S-video signal, which is transmitted to the
monitor 400. With this configuration, the image of the target
portion 10 in a relatively wide area is displayed.
[0080] It should be noted that, in the fourth embodiment, the color
CCD image is obtained in accordance with the frame sequential
method. The invention need not be limited to this configuration,
and a color CCD may also be used for capturing a color image. In
such a case, the target portion 10 is illuminated with white
light.
[0081] The confocal endoscope 1100 further includes a confocal
observing section for observing a surface image or tomography
inside the human cavity at a relatively large magnification. The
confocal observing section includes a GRIN lens 1140, an optical
fiber 1141, the polarization unit 1150, a micromirror 1153 and a
micromirror 1156.
[0082] The processing unit 1300 includes a laser source 1301, which
emits a He--Ne laser beam having a wavelength of 632 nm. It should
be noted that, when a laser source that emits a laser beam having a
shorter wavelength, a higher resolution of the image can be
achieved. Thus, the laser source 1301 need not be limited to the
He--Ne laser, but an Argon ion laser may be used instead.
[0083] Further, according to the fourth embodiment, the laser
source 1301 has a Brewster window. The laser source 1301 emits an
S-polarization laser beam with respect to the polarization layer
1151. The laser beam emitted by the laser source 1301 is
transmitted through the optical fiber 1141, which is a single mode
fiber, via a coupler 1302.
[0084] The laser beam emerged from the optical fiber 1141 is
incident on the GRIN lens 1140, which collimates the laser beam.
The collimated laser beam emerges from the GRIN lens 1140 toward
the polarization layer 1151 included in the polarization unit
1150.
[0085] The polarization unit 1150 is formed such that two
polarization beam splitting cubes are cemented. The two
polarization beam splitting cubes include a polarization layer 1151
and a polarization layer 1154, each of which is configured to
reflect an S-polarization beam and allows the P-polarization beam
to pass through. Further, on a pair of surfaces parallel to the
optical axis of the confocal endoscope 1100 and opposite to each
other, .lamda./4 plates 1152 and 1155 are cemented. Each of the
.lamda./4 plates 1152 and 1155 converts a linear polarization beam
into a circular polarization beam, and the circular polarization
beam into the linear polarization beam.
[0086] The collimated beam emerged from the GRIN lens 1140 and
incident on the polarization layer 1151 as the S-polarized beam
reflected by the polarization layer 1151 by 90 degrees and proceeds
toward the .lamda./4 plate 1152. The beam then passes through the
.lamda./4 plate 1152 and incident on the micromirror 1153 as the
circular polarization beam.
[0087] The circular polarization collimated beam incident on the
micromirror 1153 is reflected thereby, passes through the .lamda./4
plate 1152 again, and incident on the polarization layer 1151 as
the P-polarized collimated beam. Since the polarization layer 1151
allows the P-polarized beam to pass therethrough, the beam is
incident on the polarization layer 1154 as the P-polarization beam,
passes through the polarization layer 1154, and incident on the
.lamda./4 plate 1155.
[0088] The P-polarized collimated beam incident on the .lamda./4
plate 1155, passes therethrough, and incident on the micromirror
1156 as the circular polarization beam. The beam is then reflected
by the micromirror 1156, passes through the .lamda./4 plate 1155,
and incident on the polarization layer 1154 as the S-polarization
collimated beam.
[0089] Since the polarization layer 1154 reflects the
S-polarization beam, as described above, it proceeds toward the
objective lens 1110. The optical axis of the confocal probe section
and the optical axis of the surface observing section coincide with
each other. The collimated beam is converged on the target portion
10 via the objective lens 1110. With this configuration, since the
surface observing section and the confocal probe section use the
same objective lens to view the target portion 10, no parallax
occurs between the images obtained by the two optical systems.
[0090] The laser beam incident on the target portion 10 is
reflected thereby and incident on the objective lens 1110. The
objective lens 1110 collimates the reflected beam, which returns
the optical path as described above and enters the GRIN lens
1140.
[0091] As described above, the optical fiber 1141 is the single
mode fiber. Therefore, the diameter of the core is very small,
ranging from 3 to 9 .mu.m (which varies depending on the working
wavelength). An end surface 1141a of the optical fiber 1141 is
located at a position which is conjugate with the focal point on
the object side of the objective lens 1110. Thus, among the light
flux incident on the target portion 10, those converged on the
target portion 10 is converged by the GRIN lens 1140 on the end
surface 1141a of the optical fiber 1141. The light flux converged
on the end surface 1141a is transmitted through the core of the
optical fiber 1141, and received by the light receiving element
1303 through the coupler 1302.
[0092] The reflected light that is reflected on surfaces of the
target portion 10 other than the focal plane of the objective lens
1110 is not converged on the end surface 1141a, and thus does not
enter the core of the optical fiber 1141. Accordingly, such light
is not transmitted to the processing unit 1300. That is, the
optical fiber 1141 transmits only the light reflected by the target
plane 10 on the focal plane of the objective lens 1110 to the
processing unit 1300. Thus, the end surface 1141a of the optical
fiber 1141 functions as a pin hole which shields the light
reflected by surfaces other than the focal plane of the objective
lens 1110, and functions to allow the image obtained by the optical
system provided to the confocal endoscope device 1500 to the
processing unit 1300.
[0093] Further, an aperture stop (i.e., the pin hole) is provided
on a focal plane of the GRIN lens 1140, and thus the optical system
inside the endoscope device 1500 is a telecentric optical system,
which has little loss of light amount.
[0094] The light beam received by the light receiving element 1303
is converted into electrical signals corresponding to the received
light amount (i.e., image signals), which is transmitted to a
preprocessing circuit 1320. The preprocessing circuit 1320
amplifies the received signal and applies sampling/holding
procedure. Then, the output signal of the pre-processing circuit
1320 is input to an A/D converter 1321, which converts the input
image signal (analog) to a digital signal and transmits the
converted signal to a confocal image signal processing circuit
1322. The confocal image signal processing circuit 1322 is divided
into R, G and B component signals in accordance with the rotation
of the RGB filter unit 1331, and the R, G and B component signals
are stored in an RGB memory 1323. The thus stored image signals are
read out at predetermined timing, converted into analog signals by
a D/A converter 1324, and transmitted to a confocal video signal
processing circuit 1325. The confocal video signal output circuit
1325 generates video signals such as a composite video signal, an
RGB signal, or an S-video signal. The video signal is applied to
the monitor 400, thereby an image of the target portion 10 on the
focal plane of the objective lens 1110, which is captured by the
confocal image pickup section, is displayed at a high magnification
on the monitor 400.
[0095] By operating an operation panel 1340 of the processing unit
1300, an operator can selectively observe the images captured by
the confocal endoscope 1100.
[0096] Specifically, when the operator operates the operation panel
1340, signals corresponding to the operation are transmitted to a
CPU 1350. Then, the CPU 1350 controls a timing generator 1351 in
accordance with the received signal.
[0097] The timing generator 1351 drives, under control of the CPU
1350, the micromirror 1153 and the micromirror 1156 so that the
laser beam scans the target portion 10 in the X direction and the Y
direction. The reflected light on the focal plane of the objective
lens 1110 is transmitted to the processing unit 1300 as described
above.
[0098] It should be noted that, by varying a moving (scanning)
range of the micromirror 1153 and/or micromirror 1156, a field of
view of an observing image can be varied with ease. That is, when
the scanning range is smaller, an image in a small observing field
is obtained, which is displayed at a large magnification, while
when the scanning range is larger, an image within a wide area can
be obtained, which is displayed at a lower magnification. That is,
without a zooming optical system which typically includes a
plurality of groups and numbers of lenses, the magnification of the
displayed image can be changed. Since the zooming optical system is
unnecessary, the entire size of the confocal endoscope device can
be made relatively compact.
[0099] According to the fourth embodiment, the operator can select
a display method of the images on the monitor 400 by operating the
operation panel 1340. For example, the operator can switch between
the entire image of the target portion 10 using the surface
observation section, and the image captured by the confocal pickup
section. Alternatively, the entire display area of the monitor 400
is divided and both the images obtained by the surface observation
section and the confocal pickup section may be displayed. Since the
field of view of the surface observation section is relatively
wide, it can be used as a finder system for the confocal pickup
section.
[0100] In the above-described fourth embodiment, only one monitor
is employed. This configuration may be modified such that two or
more monitors are provided and the image captured by the surface
observation system (CCD) and the image captured by the confocal
pickup system are displayed in different monitors.
[0101] Conventionally, endoscopes provided with a zooming system
have been used. Typically, the conventional zooming system
electronically increases the magnification of the image. Therefore,
when the magnification is raised, the quality of the image becomes
worse. The operator is required to treat the target portion with
observing such an image having a worse quality. Thus, the operator
should be especially skilled in operating such an endoscope.
[0102] As an alternative, endoscopes provided with an optical
zooming system have been suggested. However, in such an endoscope,
a zooming optical system should be provided at the distal end
portion of the endoscope, which increases the diameter of the
endoscope. Further, in such a system, an image at a large
magnification and an image at a low magnification cannot be
observed simultaneously.
[0103] According to the fourth embodiment, it becomes possible to
obtain a large magnification image without lowering the image
quality. Further, images at the large magnification and the low
magnification can be observed simultaneously, or at least such
images are quickly switched. Therefore, operability is excellently
improved, and the target portion can be treated safely and
quickly.
[0104] The fourth embodiment may be modified such that the image of
the wide area is observed directly with the operator's eye without
using the image capturing element (CCD).
[0105] In the above-described embodiments, in order to illuminate
the target portion, the He--Ne laser is used. The invention is not
limited to this configuration, and another light having a
relatively short wavelength may be used. For example, an
ultra-high-pressure mercury lamp, which emits short-wavelength
light including near ultraviolet light, may be used as the light
source. In such a case, it becomes possible to observe fluorescent
light image of the target portion.
[0106] The present disclosure relates to the subject matters
contained in Japanese Patent Application No. 2002-321322 and No.
2002-321323, both filed on Nov. 5, 2002, which are expressly
incorporated herein by reference in their entireties.
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