U.S. patent number 6,500,114 [Application Number 09/524,746] was granted by the patent office on 2002-12-31 for method of extracting biopsy cells from the breast.
This patent grant is currently assigned to DOFI Technologies, Inc.. Invention is credited to Stanislaw Loth, Tony Petitto, Howard Worth.
United States Patent |
6,500,114 |
Petitto , et al. |
December 31, 2002 |
Method of extracting biopsy cells from the breast
Abstract
A method of extracting biopsy cells from a breast uses an
endoscopic instrument having a distal end that is substantially
needle like, a working channel, a light source and a lens. The
instrument can be coupled to an apparatus for viewing an image
including depth of field viewing. The instrument is inserted into a
nipple of a breast and liquid is ejected from the distal end.
Reverse pressure is applied so that the liquid and biopsy cells are
retrieved into the instrument. The cells are then extracted from
the breast.
Inventors: |
Petitto; Tony (Beverly Hills,
CA), Loth; Stanislaw (Sloatsburg, NY), Worth; Howard
(Venice, CA) |
Assignee: |
DOFI Technologies, Inc.
(N/A)
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Family
ID: |
27485641 |
Appl.
No.: |
09/524,746 |
Filed: |
March 14, 2000 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
Issue Date |
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115810 |
Jul 15, 1998 |
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006894 |
Jan 14, 1998 |
6067191 |
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345806 |
Nov 22, 1994 |
5774260 |
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155748 |
Nov 23, 1993 |
5400177 |
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Current U.S.
Class: |
600/156;
348/E13.071; 348/E13.033; 348/E13.014; 348/E13.058; 348/E13.044;
348/E13.004; 348/E13.04; 348/E13.022; 348/E13.038; 348/E13.034;
600/160; 600/563; 348/E13.029 |
Current CPC
Class: |
G02B
5/045 (20130101); G02B 30/40 (20200101); H01J
29/89 (20130101); H04N 13/305 (20180501); H04N
13/194 (20180501); H04N 13/341 (20180501); H04N
13/189 (20180501); H01J 2229/893 (20130101); H04N
13/337 (20180501); H04N 13/204 (20180501); H04N
13/286 (20180501); H04N 13/327 (20180501); H04N
13/361 (20180501); H04N 13/239 (20180501); H04N
13/363 (20180501); H04N 13/324 (20180501) |
Current International
Class: |
G02B
5/04 (20060101); G02B 27/22 (20060101); H04N
13/00 (20060101); H01J 29/89 (20060101); A61B
001/12 () |
Field of
Search: |
;600/563,564,565,566,112,156,128,153,160 ;604/35,44 ;348/65 |
References Cited
[Referenced By]
U.S. Patent Documents
Foreign Patent Documents
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40 06 868 |
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Sep 1991 |
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DE |
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2184286 |
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Jun 1987 |
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GB |
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WO81/01201 |
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Apr 1981 |
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WO |
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Other References
Okazaki et al., "Fiberoptic ductoscopy of the breat: A new
diagnostic procedure for nipple discharge" Jpn.J. Clin. Oncol.
(1991) 21(3):188-193.* .
Makita et al., "Duct endoscopy and endoscopic biopsy in the
evaluation of nipple discharge" Breast Cancer Research and
Treatment (1991) 18:179-187.* .
Otto W. Sartorius, et al., Cytologic Evaluation of Breast Fluid in
the Detection of Breast Disease, Journal of National Cancer
Institute, vol. 59 No. 4, Oct. 1977, pp. 1073-1080. .
Pole, R.V. et al., Real Time Computer-Generated 3-D Display, IBM
Technical Disclosure Bulletin, vol. 10, No. 5, pp. 601-603 (Oct.
1967). .
Jorma Ryhanen, Biocompatibility Evaluation of Nickel-Titanium Shape
Memory Metal Alloy (1999) (Ph.D. Thesis, University of Oulu,
Finland) (on file with the Oulu University Library) (also available
in Adobe Acrobat format online at:
http://herkules.oulu.fi/isbn9514252217/). .
Shape Memory Applications, Inc., NiTi Smart
Sheet,<http://www.sma-inc.com/biocomp.html>(visited Jan. 3,
2000). .
Susan M. Love, Sanford H. Barsky; Breast-duct endoscopy to study
stages of cancerous breast disease; The Lancet 1996: 348
997-99..
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Primary Examiner: Leubecker; John P.
Attorney, Agent or Firm: Arnold & Porter
Parent Case Text
The present application is a continuation-in-part of co-pending
U.S. Pat. application Ser. No. 09/115,810, filed Jul. 15, 1998, now
abandoned, which is a continuation-in-part of U.S. patent
application Ser. No. 09/006,894, filed Jan. 14, 1998, now U.S. Pat.
No. 6,067,191, which is a continuation-in-part of U.S. patent
application Ser. No. 08/345,806, filed Nov. 22, 1994, by Tony
Petitto and Stanislaw Loth, for "Technique for Depth of Field
Viewing of Images With Increased Clarity and Contrast," now U.S.
Pat. No. 5,774,260, which is a continuation-in-part of U.S. patent
application Ser. No. 08/155,748, filed Nov. 23, 1993, by Tony
Petitto and Stanislaw Loth, for "Technique for Depth of Field
Viewing of Images With Improved Clarity and Contrast," now U.S.
Pat. No. 5,400,177, hereby incorporated by reference in their
entirety.
Claims
What is claimed is:
1. A method of extracting biopsy cells from a body using an
endoscopic instrument having a distal end that is sub statially
needle like, said method comprising the steps of: (a) inserting
said instrument into a nipple of a breast; (b) causing liquid to be
ejected from the distal end of said instrument; (c) causing reverse
pressure to form at the distal end of such instrument so that said
liquid and biopsy cells are retrieved into said instrument; and (d)
extracting said cells from said breast, wherein the endoscopic
instrument includes a guide having a working channel, a light
source and a lens.
2. The method of claim 1, wherein step (a) includes: projecting an
image of the interior of said breast on a video monitor.
3. A method of extracting biopsy cells from a body using an
endoscopic instrument having a distal end that is substantially
needle like, said method comprising the steps of: (a) inserting
said instrument into a nipple of a breast; (b) causing liquid to be
ejected from the distal end of said instrument; (c) causing reverse
pressure to form at the distal end of such instrument so that said
liquid and biopsy cells are retrieved into said instrument; and (d)
extracting said cells from said breast, wherein the endoscopic
instrument includes a guide having a working channel, a light
source and a lens, said guide coupled to means for receiving a
medical instrument, to means for irrigating and to means for
supplying image information image, and wherein the endoscopic
instrument also includes a video camera coupled to a video
monitor.
4. The method of claim 3, wherein said video monitor is coupled to
an aspherical lens.
5. The method of claim 4, wherein a first radius of said aspherical
lens blends into a second radius of said aspherical lens.
6. The method of claim 4, wherein said aspherical lens is comprised
of more than 2 radii.
7. The method of claim 3, wherein step (a) includes: projecting an
image of the interior of said breast on said video monitor.
8. A method of extracting biopsy cells from a body using an
endoscopic instrument having a distal end that is substantially
needle like, said method comprising the steps of: (a) inserting
said instrument into a nipple of a breast; (b) causing liquid to be
ejected from the distal end of said instrument; (c) causing reverse
pressure to form at the distal end of such instrument so that said
liquid and biopsy cells are retrieved into said instrument; and (d)
extracting said cells from said breast, wherein the endoscopic
instrument is coupled to an apparatus for depth of field viewing,
said apparatus including: a transparent screen for positioning
between a flat image and a viewer, said transparent screen
including a plurality of optical elements formed in said screen;
and an aspherical lens for positioning between said screen and a
viewer, said lens being curved across its width which curvature is
defined by at least two radii.
9. The method of claim 8, wherein a first radius of said aspherical
lens blends into a second radius of said aspherical lens.
10. The method of claim 8, wherein said aspherical lens is
comprised of more than 2 radii.
11. A method of extracting biopsy cells from a body using an
endoscopic instrument having a distal end that is substantially
needle like, wherein the endoscopic instrument is coupled to a
video camera and a video monitor, said method comprising the steps
of: (a) inserting said instrument into a nipple of a breast; (b)
causing liquid to be ejected from the distal end of said
instrument; (c) causing reverse pressure to form at the distal end
of such instrument so that said liquid and biopsy cells are
retrieved into said instrument; and (d) extracting said cells from
said body, wherein the endoscopic instrument includes a guide
having a working channel.
12. The method of claim 11, wherein the endoscopic instrument
further includes a light source and a lens, and wherein the guide
is coupled to a biopsy tube, an irrigation channel, and to a video
port.
13. A method of extracting biopsy cells from a body using an
endoscopic instrument having a distal end that is substantially
needle like, said method comprising the steps of: (a) inserting
said instrument into a nipple of a breast; (b) causing liquid to be
ejected from the distal end of said instrument; (c) causing reverse
pressure to form at the distal end of such instrument so that said
liquid and biopsy cells are retrieved into said instrument; and (d)
extracting said cells from said body, wherein the endoscopic
instrument is coupled to an apparatus for depth of field
viewing.
14. The method of claim 13, wherein the apparatus for depth of
field viewing includes: a transparent screen for positioning
between a flat image and a viewer, said transparent screen
including a plurality of optical elements formed in said screen.
Description
BACKGROUND OF THE INVENTION
Depth of field viewing, as described in U.S. Pat. No. 5,400,177, is
accomplished by enhancing depth cues which are present in every
flat image, whether photographed or recorded electronically,
without the requirement of special glasses, eye shutters or similar
devices used in front of the viewers eyes. The depth cues are
enhanced by a specially designed prismatic screen that separates
the viewer's eye focus and convergence. The separation triggers the
brain of the viewer to disregard convergence information indicating
that the screen is flat, and to interpret the image depth cues as
real.
To strengthen the focus and convergence separation and add
additional image magnification, the present invention utilizes a
specially designed magnifying lens as a supplement to the prismatic
screen. The lens helps trigger the eye focus and convergence
separation--making it stronger when combined with a prismatic
screen such as is disclosed in U.S. Pat. No. 5,744,260. In
addition, depending upon the particular design of the lens, the
viewed image may magnified from 1.25.times. to 2.0.times., and at
the same time is cleared (cleaned) from the magnified raster of the
video scanning lines. The clearing (cleaning) of the viewed image
from the magnified raster is accomplished with the prismatic
screen, as described in the parent application. With particular
reference to FIGS. 29 to 36 of that application, the prismatic
screen PR preferably includes three miniature prisms for each video
scan line. As a result, each raster video scan line is divided two
or three times, thereby providing a significant reduction in the
visibility of the raster lines. In accordance with the present
invention, as described in greater detail below, the prismatic
screen may be either a flat or curved structure, depending upon the
choice of additional optical elements in the system.
A number of designs on how to magnify a video small screen image to
a larger screen image are described in patent literature. For
example U.S. Pat. Nos. 2,449,886 and 5,061,052 disclose such
systems. Each of these designs are based on using a positive lens,
or a lens combined with a Fresnel lens, and each technique places
the optical system near the front of the video monitor screen. The
lenses are designed with a short focal length which may cause
distortion, because the magnification of the image is not equal in
the center and on the edges. Additionally, the Fresnel lens, which
is a concentric design of a magnifying lens, may cause image
degradation by lowering the image resolution. According to U.S.
Pat. No. 5,061,052, the described system is intended to allow
individuals of limited means to enjoy the entertainment and
education provided by large screen television images, without the
necessity of purchasing a large television set. However, such prior
art television magnification of a small screen image to a larger
screen image may cause distortion and a poor image, particularly
since these systems magnify the raster of scanned video lines which
make up the image. When the lines are magnified, the image is
degraded and becomes distorted, and eyestrain may result. These and
other disadvantages of the prior art are overcome by the present
invention.
Recently, video monitoring and imaging technology has made its way
into the operating room and the physician's office. One example of
such medical uses for this technology includes the optical
connection of a video camera and monitoring device to an endoscope
or similar instrument that is adapted with fiber optics. Such
instruments are used to perform medical procedures, such as
biopsies, on internal organs without the need for extremely
invasive surgery. They usually comprise a longitudinally extending
hollow tube made of plastic or metal that is inserted into the body
through an orifice or incision. A smaller passageway is included in
the channel of the tube longitudinally, through which a medical
instrument of some type, such as a biopsy brush or scrape, may be
inserted for performing various procedures on the internal organ of
interest. The physician, using a handle at the proximal end of the
medical instrument, may manipulate the instrument as desired.
Such instruments have in the past involved a number of drawbacks.
For example, because the instrument is inserted into the patient's
body, it has been difficult to accurately view how the procedure is
progressing. Some scopes have included fiber optic strands that
allow the physician to see an image of the organ or tissue being
treated. However, because of the small areas involved and the
limited amount of light in such areas, such images have been of
poor quality and limited use.
The dimensions of the scope have also often been too large. In
order to minimize the invasiveness of the procedure, and therefore
the pain and discomfort of the patient, the physical dimensions of
the endoscope and its various parts are best minimized.
Furthermore, many cavities of the human body are extremely small or
difficult to get to and are incapable of receiving prior art scopes
without damage to the surrounding tissue.
In addition, conventional biopsy brushes or other instruments used
for cytological procedures in these small body cavities do not have
the necessary flexibility or strength to provide for sufficient
scraping and/or removal of cells from papillomas or other
abnormalities.
BRIEF OBJECTS AND SUMMARY OF THE INVENTION
It is therefore an object of this invention to provide an endoscope
that is capable of being used in many of the smallest cavities of
the human body in various different procedures while generating an
image of the area of the body being treated, which image has
increased clarity and depth of field viewing.
The present invention satisfies these and other objects through the
provision of an endoscope capable of being coupled to a video
monitor adapted with a prismatic screen. The endoscope provides a
view into the smallest cavities of the body and the monitor and
screen project the image to the viewer with enhanced clarity and
depth cues. The present invention further provides a stepped
aspherical lens and a method of making the same for further
increasing the quality of depth of field viewing.
It is another object of the present invention to facilitate removal
of cells, tissue or other materials from the body. The present
invention satisfies this and other objects through the provision of
a Nitinol cytology instrument having improved strength and
biocampatibility characteristics.
In one aspect, the present invention relates to a system including
an endoscope comprising a guide having a working channel, a light
source and a lens, said guide coupled to means for receiving a
medical instrument, to means for irrigating and to means for
supplying a video image. The endoscope is preferably coupled to a
video camera, the video camera is preferably coupled to a video
monitor. The video monitor is preferably coupled to a transparent
screen which includes a plurality of generally parallel microprisms
formed in the screen and extending horizontally across the width of
the screen, said screen also coupled to an optical element operable
to adjust the paths of light transmitted through said screen.
In another aspect, the present invention relates to a system
including an instrument for retrieving biopsy cells from a body
coupled to an apparatus for depth of field viewing. The apparatus
includes a transparent screen for positioning between a flat image
and a viewer, said transparent screen including a plurality of
optical elements formed in said screen and an aspherical lens for
positioning between said screen and a viewer, said lens being
curved across its width which curvature is defined by at least two
radii.
In another aspect, the present invention relates to a method of
inspecting a breast with an endoscopic instrument wherein said
endoscopic instrument includes a guide having a working channel, a
light source and a lens; a first tube having a biopsy channel; a
second tube having an irrigation channel; a third tube having an
interior passageway; and a medical instrument for inserting into
said biopsy channel and said working channel. The method includes
inserting the distal end of said medical instrument into the
dilated nipple of said breast and projecting an image of the
interior of said breast on a video monitor.
In another aspect, the present invention relates to a method of
extracting biopsy cells using an endoscopic instrument having a
distal end that is substantially needle like. The method includes
inserting said instrument into a body and causing liquid to be
ejected from the distal end of said instrument. The method further
includes causing reverse pressure to form at the distal end of such
instrument so that said liquid and biopsy cells are retrieved into
said instrument and extracting said cells from said body.
In yet another aspect, the present invention relates to a method of
performing a medical procedure on the interior of a blood vessel
using an endoscope having a substantially flexible guide of a
length greater than one meter and which is optically coupled to a
video monitor. The method includes inserting said guide into a
blood vessel and projecting an image of the interior of said blood
vessel on said video monitor.
In another aspect, the present invention relates to a method of
clearing a clogged area in a lacrimal duct using an endoscope that
includes a guide having an outer diameter of not more than about
1.2 mm and a working channel defined therein having an outer
diameter of not more than about 0.35 mm, a first tube portion
coupled to said guide having a biopsy channel defined therein; said
biopsy channel being capable of receiving a medical instrument, a
second tube portion coupled to said guide and having an irrigation
channel defined therein, and a third tube portion coupled to said
guide and having defined therein an interior passageway for holding
fiber optic strands. The method includes inserting said guide into
the lacrimal duct of a patient and projecting an image of the
interior of said duct on a video monitor. The method also includes
identifying the clogged area and clearing said area with a
laser.
In another aspect, the present invention relates to a method of
treating a tumor in an interior cavity of a body using an
endoscopic instrument comprising a guide having a working channel,
a light source and a lens; a first tube having a biopsy channel;
said first tube coupled to said guide; a second tube having an
irrigation channel; said second tube coupled to said guide; a third
tube having an interior passageway; said third tube coupled to said
guide; and a medical instrument for inserting into said biopsy
channel and said working channel; said medical instrument being
substantially needle like at its distal end. The method including
inserting said guide into said cavity to approximately the position
of the tumor and projecting an image of said tumor onto a video
monitor. The method also includes injecting a chemotherpuetic
liquid directly into said tumor by forcing said liquid through said
irrigation channel and said working channel.
In yet another aspect, the present invention relates to a method of
performing a medical procedure on the interior of a body using an
endoscope coupled to a video monitor, said video monitor being
coupled to a transparent screen which includes a plurality of
generally parallel microprisms formed therein, said microprisms
extending horizontally across the width of the screen, said screen
coupled to an optical element operable to adjust the paths of light
transmitted through said screen. The method includes inserting said
endoscope into said body and projecting an image of the interior of
said body on said screen.
In another aspect, the present invention relates to a system
including an endoscope, a video monitor coupled to said endoscope,
and an aspherical lens coupled to said video monitor.
In another aspect, the present invention relates to a system
including means for examining the interior of a bodily cavity or
hollow organ and means for displaying a video image coupled to said
means for examining the interior of a bodily cavity or hollow
organ. The system also includes aspherical lens means coupled to
said means for displaying a video image, said aspherical lens means
configured for adjusting the path of light transmitted through said
means for displaying a video image.
In yet another aspect, the present invention relates to a method of
viewing the progress of a medical procedure comprising the steps of
generating an image of the interior of a bodily cavity or organ,
displaying the image on a video monitor, and passing the image
through an aspherical lens.
In another aspect, the present invention relates to a system
including an endoscope having a 0.35 mm working channel, a video
monitor coupled to said endoscope, and an optical element, wherein
said video monitor is coupled to said optical element.
In another aspect, the present invention relates to a system
including an endoscope, a cytology instrument, wherein said
cytology instrument is slidably and releasably coupled within said
endoscope, a video monitor coupled to said endoscope, and an
optical element, said optical element coupled to said video
monitor.
In another aspect, the present invention relates to a system
including an endoscope for examining the interior of a bodily
cavity or hollow organ, a video monitor coupled to said endoscope
for displaying a video image, and a stepped aspherical lens coupled
to said video monitor, said stepped aspherical lens configured to
adjust the path of light transmitted through said video
monitor.
In another aspect, the present invention relates to a method for
making a stepped ashperical lens from a lens material, including
the steps of cutting a plurality of radii steps into a surface of
the lens material and polishing the plurality of radii steps.
In another aspect, the present invention relates to a cytology
instrument for removing cells from a bodily material comprising a
longitudinally extending main body portion having a proximal and a
distal end, said distal end having a roughened surface and wherein
said main body portion has a diameter of up to about 0.30 mm.
In yet another aspect, the present invention relates to a method of
retrieving cells from a bodily material using a cytology instrument
having a diameter of up to about 0.30 mm. The method comprising
inserting the cytology instrument through a working channel of an
endoscopic device and scraping a surface of a targeted bodily
tissue to remove material from the surface. The method also
includes injecting a fluid through an irrigation channel of an
endoscopic device, wherein the fluid mixes with the material
removed from the surface forming a fluid-material mixture and
removing the cytology instrument from the working channel. The
method further includes aspirating the fluid-material mixture
through the working channel.
BRIEF DESCRIPTION OF THE DRAWINGS
The foregoing objects, as well as additional objects, features and
advantages of the present invention, will be apparent from the
following detailed description when read in light of the
accompanying drawings, wherein:
FIG. 1 is an illustration of the present invention including the
magnifying lens 4;
FIG. 2 is an illustration of how a piano convex lens magnifies an
image;
FIG. 3 is an illustration of how the piano convex lens magnifies
the video image in accordance with one aspect of the present
invention;
FIG. 4 is an illustration of how the magnifying lens 4 enhances the
depth cues of the viewed video image;
FIG. 5A is an illustration of the location of the prismatic screen
in front of the video screen as illustrated in U.S. Pat. No.
5,400,177;
FIG. 5B is an illustration of one embodiment of the present
invention with the lens 4 placed in front of the prismatic
screen;
FIG. 5C is an illustration of an embodiment of the present
invention with the lens 4 and the curved prismatic screen "PR" in
place;
FIG. 5D is an illustration of an embodiment of the present
invention with the lens 4 and the prismatic screen "PR" applied to
the plano surface of lens 4;
FIG. 5E is an illustration of an embodiment of the present
invention with the light pass "e" passing the lens L4 and the
single prism of the prismatic screen "PR";
FIG. 5F is an illustration of an embodiment of the present
invention wherein the light path "e" passes angled lens 4 and a
single prism of a prismatic screen PR laminated to the lens;
FIG. 5G is another illustration of an embodiment with a prismatic
screen laminated to the lens 4, wherein the angles of the prism and
the lens 4 have been changed from those of FIG. 5F;
FIG. 6A is an illustration of an embodiment of the present
invention with the lens 4 made in BK7 glass;
FIG. 6B is an illustration of another embodiment of the present
invention with the lens 4 made with high refraction index SK16
glass;
FIG. 7 is an illustration of yet another embodiment of the present
invention with the lens 4 designed as a hollow optical structure
which is filled with a liquid high refraction index filler;
FIG. 8 is an illustration of the present invention with the lens 4
replaced by a parallel transparent plate;
FIG. 8A is an illustration of an embodiment of the present
invention with the prismatic screen "RP" placed behind the
transparent plate;
FIG. 9 is an illustration of the present invention with the
prismatic screen "PR" attached to the parallel transparent
plate;
FIG. 9A is an illustration of the present invention with the
parallel transparent plate demonstrating how the viewers eyes see
the virtual video image S2, which appears in front of the video
screen S1;
FIG. 10 is an illustration of the present invention with the
parallel transparent plate which is hollow and is filled with a
liquid high refraction index filler;
FIG. 11 is an illustration of two viewing points along the center
axis of a video monitor with a depth of field prismatic screen and
a spherical magnifying lens attached thereto;
FIG. 12 is an illustration of a viewing point shifted to one side
of the center axis of a video monitor with a depth of field
prismatic screen and a spherical magnifying lens attached
thereto;
FIG. 13 is an illustration of a viewing point shifted to one side
of the center axis of a depth of field prismatic screen and an
adjacent spherical magnifying lens;
FIG. 14 is an illustration of a depth of field prismatic screen and
an adjacent aspherical magnifying lens;
FIG. 15 is an illustration of two viewing points along the center
axis of a depth of field prismatic screen and an aspherical
magnifying lens;
FIG. 16 is an illustration of a viewing point shifted to one side
of the center axis of a depth of field prismatic screen and an
aspherical magnifying lens;
FIG. 17 is an illustration of two viewing points along the center
axis of a depth of field prismatic screen and an aspherical
magnifying lens as those viewing points are related to left and
right eye inter ocular distance;
FIG. 17a is an illustration of an exemplary aspherical lens
designed to account for the interocular distance between the eyes
of a viewer;
FIG. 18 is an illustration of the reduction in lens thickness
corresponding to use of an aspherical magnifying lens in the
present invention;
FIG. 19 is an illustration of three viewing points, one along, one
above and one below the center axis of a depth of field prismatic
screen and an aspherical magnifying lens;
FIG. 20 shows one example of the prismatic screen of the present
invention used in the context of a computer monitor;
FIG. 21 shows an aspherical lens having defined therein 50 or more
radii that blend on into the other;
FIG. 22 shows an aspherical lens magnifying a computer image;
FIG. 23 shows the prismatic screen and aspherical lens placed in
front of a computer monitor screen;
FIG. 24 shows a computer monitor screen framed with a liquid
crystal screen;
FIG. 25 is a side elevational view of one embodiment of the
endoscope of the present invention;
FIG. 26 is a cross-sectional view of the guide of the endoscope of
the disclosed embodiment;
FIG. 27 is a side elevational view of one embodiment of the biopsy
tube of the present invention;
FIG. 28 is a side elevational view of the endoscope of the
disclosed embodiment coupled to a syringe for biopsy cell
extraction and to video equipment for increased depth of field
viewing;
FIG. 29 is a side elevational view of a molding step in a method
for forming a stepped aspherical lens in accordance with the
present invention;
FIG. 30 is a side elevational view of a cutting step in a method
for forming a stepped aspherical lens in accordance with the
present invention;
FIG. 31 is an illustration of a preferred step arrangement on a
lens in an embodiment of the present invention;
FIG. 32 is a side elevational view of a stepped aspherical lens of
the present invention;
FIG. 33 is a side elevational view of a stepped aspherical lens of
the present invention;
FIG. 34 is an illustration of varying radii of a stepped aspherical
lens of the present invention;
FIG. 35 is a side elevational view of a polishing step in a method
for forming a stepped aspherical lens in accordance with the
present invention;
FIG. 36 is a top elevational view of a stepped aspherical lens of
the present invention;
FIG. 37 is an illustration of a conventional endoscope employing a
1/2 inch video camera chip;
FIG. 38 is an illustration of an embodiment of the present
invention employing a 1/4 inch video camera chip; and
FIG. 39 is an illustration of an embodiment of the depth of field
viewing system of the present invention employing the 1/4 inch
video camera chip.
DETAILED DESCRIPTION
Although the present invention is described below in connection
with specific embodiments, it will be appreciated that the
invention is not limited to the described embodiments. For example,
portions of the present invention are housed and the optical
elements are aligned with high precision in a frame that is
constructed in height and width to be attached to the front of any
existing video monitor. However, other techniques for housing and
mounting the optical elements may also be used. Moreover, other
portions of the invention are describing as being of various
dimensions, forms and uses. However, except as specifically
claimed, the invention is not intended to be so limited.
The present invention, when attached to a 19" or 13" medical video
monitor, is designed to permit the viewer to observe the 2"
diameter, micro endoscopic image as described in application Ser.
No. 08/155,748, magnified 1.25.times. to 2.0.times.. The image also
appears to the viewer with improved resolution, with enhanced image
detail and image depth cues, which are not recognizable in a less
detailed video image.
In Laparoendoscopic/Endoscopic surgery procedures, the video image
is transmitted directly from the inside of the patient's body to a
19" or 13" video monitor. Of particular importance is Micro
Endoscopic procedures that are viewed through a micro fiber optic
image conduit. The image is typically taken in a relatively low
light environment, and the final image that appears on the 19"
medical monitor is only 2" in diameter and is often noisy and
characterized by relatively poor resolution quality.
Micro Endoscopic procedures for the Parotid tear duct, Lacrimal
tear duct, breast exploration and reconstructive surgery, disorders
of the spine, Neurosurgery of the brain and nerve system, inner
ear, nose and throat (Otolaryngology), reconstructive plastic
surgery, Fallopascopy, Gynecology, reproductive genetics and
minimally invasive veterinary surgery are performed using scopes
with fiber optic bundles that range in diameter from 0.3 mm to 3.0
mm. These difficult procedures have opened new avenues of
improvement on surgery of the human body. Such procedures eliminate
the need to open large operation areas and allow one to reach into
and see inside very small and narrow body ducts. It also reduces
the patient's trauma, stress, danger of infection, and allows the
patient in most cases to recover quickly.
With all the latest improvements in the lens, fiber optic, video
camera, high-resolution video monitor and actual technique in the
different micro procedures the image quality transmitted to the
video monitor often remains poor. The relatively poor quality is
not only caused by the small size of the viewed image, but also
results from poor sharpness and clarity of the image. This is the
result of the lens at the end of the fiber optic conduit being only
a minimum 1/50th of an inch in diameter of the environment in which
the image is taken.
The 2" micro image transmitted through the fiber optic is focused
into the video camera as a relatively small and dark image. The
image is only 1/6th of the height of a 19" monitor screen, and
occupies only 1/40th of the monitor screen surface. However, the
19" monitor is the monitor of choice for most surgeons for Micro
Endoscopic procedures because on the 13" monitor the micro image is
only 1.25" in diameter. It is often very difficult to perform micro
procedures with such a small image.
Both the 19" and 13" medical video monitor images are constructed
with the same components, the video image pixels (small electronic
dots which form the raster of scanning lines which form the image).
Both 19" and 13" basic video monitors contain the same amount of
200 scanning resolution lines. A raster scanning line, which runs
the width of the video screen, is approximately 1.0 mm high, 1/25th
of an inch; and the space between the raster lines is normally 0.5
mm, 1/50th of an inch. The thickness of the lines and the space
between the lines creates 200 scanning lines of basic image
resolution that fills, top to bottom, the video monitor screen.
In comparing the video image with a film image, the video image
resolution is as much as 15 times lower. Quality photographic
lenses are usually manufactured with 100 times better resolution
(100 lines per 1.0 mm).
Normal endoscopic video systems project the image to the full size
of the video screen. This is because they are not restricted to the
1/24th of an inch diameter of the fiber optic light conduit and are
equipped with a powerful light source to illuminate the viewing
area. This, however, is impossible to achieve with the micro
endoscopic imaging systems.
The micro endoscopic video system is an electronic and optical
breakthrough in surgical technique that allows the small, confined
areas of the human body like the tear duct and the spinal canal to
be imaged. However, the poor image quality and its 2" diameter size
have limited its application and effectiveness. It is for this
reason that the present invention achieves significant improvement
over the deficiencies of prior art television screen magnification
screen systems and is an extension to micro endoscopic technology,
which helps solve the surgeon's needs for an enlarged, enhanced
quality, depth of field image as viewed on the video monitor
screen.
Referring now to FIG. 1, a 19" video monitor 1, includes a video
screen 2. A housing 5 is attached in front of the video screen 2,
and contains the mounted depth of field prismatic screen 3. The
screen 3 is assembled in a frame 3A. As described in application
Ser. No. 08/155,748, now U.S. Pat. No. 5,400,177, the depth of
field screen is a multi prismatic structure with a plurality of
horizontal micro prisms which extend across the width of the inner
surface of the depth of field screen 3. Particular reference is
made to FIGS. 5-12, 25-36 and 39 of that patent and the
accompanying written specification for a more detailed description
of the depth of field screen.
In one embodiment of the present invention, a magnifying lens 4
placed in the front portion of the housing 5 provides stronger
depth cue enhancement and magnifies the image for easier viewing.
In relation to the 2" diameter micro image, the magnification does
not exceed 2.0.times.. In relation to a fall screen video image,
the magnification does not exceed 1.25.times.. In accordance with
the present invention, the prismatic screen 3 and the lens 4 are
designed as a single optical system. Without the prismatic screen,
the lens 4 would magnify the image as well as the raster scan
lines, making the image unacceptable. The prismatic screen as
described in application Ser. No. 08/155,748 without the lens 4,
does not magnify the image 1.25.times. to 2.0.times..
The housing 5 attaches the optical elements to the front of the
video monitor. Preferably, the front and rear portions of the
housing are sealed with front and rear tempered glass windows,
respectively, which are treated with anti-reflection coatings. The
lens 4 may be an acrylic plano convex lens which is designed to
provide focus and convergence separation. The focal length of the
lens 4 is relatively long, preferably about 30 inches, but
advantageously may range from 10" to 40". The lens 4 is preferably
mounted about 5 inches from the video screen.
The prismatic screen 3, described fully in parent application Ser.
No. 08/155,748 (incorporated herein by reference) is placed between
the lens 4 and the video screen to provide additional focus and
convergence information, and to reduce the size of video raster
lines by three times. The prismatic screen is preferably mounted
near the video screen with the "rows" of prism lenses running
parallel to the video scan lines. The interior portion of the
housing is preferably blackened to separate the viewed image from
ambient light and reflections, which also helps to strengthen depth
cues. Preferably, the outside front portion of the housing includes
a black frame which tilts the optical front window by approximately
50 degrees to 100 degrees toward the inside of the housing to help
eliminate reflections of bright objects and ambient light that may
be present in front of the glass window.
The manner in which viewers eyes perceive depth cues is described
in application Ser. No. 08/155,748 with particular reference to
FIGS. 13 to 22. In the same application, the manner in which the
prismatic screen reduces the raster of video scanning lines is
described with reference to FIGS. 31 to 36B. In the present
invention, the plano convex lens 4, when combined with the
prismatic screen also serves as a depth cue enhancement lens. The
screen 3 and the lens 4 are designed as a single optical system
3-4.
FIG. 2 illustrates how a plano convex lens magnifies a video image.
A viewed object O.sub.1 is magnified by the lens L to provide a
magnified object image O.sub.2. In one embodiment, the eye viewing
distance to the lens is variable and the focal length of the lens
is preferably a relatively long focal length.
FIG. 3 illustrates how the long focal length lens is used in the
present invention. In one embodiment, the magnification of the
video screen S1, to the virtual image S2, is accomplished with a 25
inch diameter lens having a focal length of 762 mm and placed at
the distance of 126 mm from the video screen. Since the primary
object in the design of the lens is to strengthen the depth cues in
the video image, the magnification can be kept as low as about
1.25.times., which is below the distortion range caused by image
magnification.
FIG. 4 illustrates the manner in which depth cues are enhanced.
When a light beam passes through a transparent structure of glass
or plastic, depending on the refraction index and the thickness of
the structure, the image will focus at a shorter distance. When the
structure is a plano convex lens, the image will be focused at a
shortened distance "a" at the center of the lens, where the lens is
thicker. Light passing through the thinner peripheral portions of
the lens will be focused at "b". By using BK7 glass, which has a
refraction index of 1.5163, the effective length of the light beam
is shortened by about 1/3 of the BK7 glass thickness, and less at
the edge of the lens.
A planar image p at the location of the screen S1 is seen through
the lens 4 as a slightly curved image S2. This added curvature
separates focus and convergence distances perceived by the eye and
enhances the depth cues present in the planar image. As shown in
FIG. 4, a light beam a passing through the central portion of the
lens 4 encounters a lens thickness t.sub.a. On the other hand, the
light beam b passes through a peripheral portion of the lens 4
having a reduced thickness t.sub.b. The lens causes focus
displacing (shifting) across the image of BK7 glass approximately
X=t.sub.a /3-t.sub.b /3. The shifting "X" causes an inconsistent
reading of the eye focus and convergence relative to the planar
video image p.
The image shifting caused by the lens provides a similar effect to
the prismatic screen as described in application Ser. No.
08/155,748. The lens and the prismatic screen combined into a
single optical system causes an increased focus and a convergence
displacement, which cuts off the convergence ability of the eyes to
indicate to the viewer that the video image is flat. This allows
the brain to analyze the depth cues to be perceived as real
depth.
FIG. 5A illustrates the arrangement in application Ser. No.
08/155,748 of the prismatic screen PR, the video screen S1 and the
virtual image S2. The virtual image S2, appears behind the video
screen S1, shifted down by the angle alpha. This image shifting is
also related to the tilt of the prismatic screen angle beta. A
typical value for the angle beta would be approximately 60.
FIG. 5B illustrates the optical system of FIG. 5A combined with the
lens L into a single optical system. The resultant virtual image S2
is magnified, causing a stronger focus and convergence
displacement, and therefore a stronger depth cue effect
enhancement. In addition, as described in the parent application,
particularly with reference to FIGS. 29 to 36b, the prismatic
screen PR preferably includes three miniature prisms for each video
scan line. As a result, each raster video scanning line is divided
into three, thereby providing a significant reduction in visibility
of raster video scanning lines.
FIG. 5C illustrates a design configuration similar to that shown in
FIG. 5B, but the prismatic screen PR is curved from side-to-side
along the horizontal axis. To accommodate the curved prismatic
screen PR, the lens L is changed from spherical to non-spherical,
and is designed to follow the curve of the prismatic screen. This
arrangement corrects image distortions for an increased angle of
viewing of the image.
FIG. 5D illustrates a side view of another configuration similar to
the arrangement of FIG. 5B. As shown in FIG. 5D, the prismatic
screen PR may be applied directly to the plano surface of the plano
convex lens L by any known technique. For example, the micro prisms
may be etched, rolled or milled with high precision directly in the
surface of the lens 4. Alternatively, the prisms could be
mechanically or chemically attached appropriately to the lens. S1
is the video image, S2 is the magnified video image.
FIG. 5E illustrates the light beam path being directed by the lens
4 and by a single prism section of the prismatic screen PR. The
light beam from the lens 4 enters the prism on the angle beta,
thereby modifying the prismatic screen's design angle alpha,
according to the focal length and the refraction index of the lens
4.
FIG. 5F shows a section of lens 4 which is laminated, cemented,
rolled, etched or milled directly to the prismatic screen PR. For
clarity, only a section of the prismatic screen is illustrated. The
prismatic screen has a prism angle of 45 degrees and the plano
surface of the lens 4 is tilted 60 degrees from the viewing axis.
FIG. 5G illustrates an alternative embodiment wherein the prismatic
screen PR has a prism angle of 60 degrees and the piano surface of
the lens is tilted 75 degrees from the viewing axis. Assuming a
horizontal viewing axis, the lens 4 is preferably placed in a more
upright position as the prism angle increases.
FIGS. 6A, 6B and 7, show different designs of the lens 4. FIG. 6A
illustrates the same lens 4 described in connection with the system
of FIG. 5B. In FIG. 6B, the lens 4, instead of being made from BK7
glass (having a refraction index of 1.5163), is made with SK16
glass which has a higher refraction index of 1.6204. The lens also
can be made from acrylic and polycarbonate plastic materials having
a relatively high index of refraction. By using a material with a
higher refraction index the center thickness (FIG. 6B) and
therefore the weight of the lens can be reduced.
FIG. 7 illustrates a design of a hollow piano convex lens which is
similar to the lens in FIG. 5B. The lens is manufactured as an
empty, molded, cut and polished element which is then filled with a
high refractive index liquid and sealed. Even with difficulties in
sealing the edges to prevent leaking of the high index liquid, this
design is still cost efficient and reduces the weight of the entire
system.
Referring now to FIG. 8, when magnification of the video image is
not desired or needed, the lens 4 may be replaced with an optically
flat plate F having a thickness, for example, of 1 inch. The thick
plate operates in a manner similar to the lens 4 by shortening the
length of the light beam passing through the transparent plate by
approximately 1/3 of the glass thickness; X=D.sub.1 -D.sub.2. As
illustrated in FIG. 8A, the virtual image S2 appears in front of
the video screen S1. As with the systems utilizing the piano convex
lens, the system of FIG. 8A causes a focus and convergence
displacement which enhances the depth cues of the viewed image.
FIGS. 9 and 9A illustrate the plate from FIG. 8 with the prismatic
screen surface PR, applied to the flat surface of the transparent
plate F. FIG. 10 shows the optically flat plate replaced by a
hollow molded or cut plate that is filled with a high refraction
index liquid and sealed.
Use of an aspherical lens in the present invention to diminish or
remove distortion will now be described in relation to FIGS. 11
through 19.
FIG. 11 illustrates a top view of one embodiment of the depth of
field viewing apparatus of the present invention, comprising video
monitor 100, video monitor screen 101, prismatic screen housing
102, prismatic screen 103 and spherical magnifying lens 104. FIG. 1
also illustrates two separate viewing points, A and B, along the
center axis O-O1 of the device. Viewing point A is at a distance FD
from spherical magnifying lens 104. Viewing point B is at a
distance CD from lens 104.
A viewer at viewing point A would see light beams along paths L1
and L2 exiting the spherical magnifying lens 104 at angles <L1
and <L2, respectively. A viewer at viewing point B would see
light beams along paths L3 and L4 exiting the spherical magnifying
lens 104 at angles <L3 and <L4, respectively. Because the
lens is spherical and these viewing points are on the center axis
of the device, the angles created by light beam paths L1 and L2 are
equal. Similarly, the angles created by light beam paths L3 and L4
are equal. Thus, the magnification of those light beams along those
paths by the spherical magnifying lens is equal and the viewer sees
little or no image distortion due to the lens.
FIG. 12 illustrates the device of FIG. 11, again having video
monitor 100, video monitor screen 101, prismatic screen housing
102, prismatic screen 103 and spherical magnifying lens 104. FIG.
12, however, shows viewing point C at a distance CD from the
magnifying lens 104 and shifted a distance S to the left of center
axis O-O1. A viewer at point C sees light beams exiting the
spherical lens 104 along paths L5 and L6 and creating angles <L5
and <L6, respectively. Unlike light viewed at points A and B as
described with respect to FIG. 11, angles <L5 and <L6 are not
equal. The magnification of light along paths L5 and L6 is
therefore different and may cause significant image distortion.
FIG. 13 is a more detailed view of the spherical magnifying lens
104 and prismatic screen 103 of FIGS. 11 and 12. There it can be
seen that the curvature of the lens 104 is defined by the radius R1
of that lens and determines the angles <L5 and <L6 associated
with light viewed by the viewer at viewing point C. As described
above, where <L5 and <L6 are different, the image seen by a
viewer at point C may be distorted.
An advantageous way to avoid or minimize this problem is to replace
the spherical magnifying lens 104 of FIGS. 11 through 13 with an
aspherical lens defined by multiple radii. FIG. 14 illustrates such
an aspherical lens 105 along with prismatic screen 103 and having
center axis O-O1. In one embodiment, aspherical lens 105 magnifies
the image created by the screen 1 to 2 times without distortion.
Aspherical lens 105 is made up of center section S1 and side
section S2. The curvature of the lens along the center section S1
is defined by radius R1, which is the same radius that defines
spherical magnifying lens 104 in FIGS. 11 through 13. The curvature
of the lens along the side section S2 is defined by radius R2,
which most advantageously is 10 to 50 percent greater than radius
R1 (as indicated by dotted line 400, which depicts what the
curvature of a spherical lens defined by radius R1 would be in
section S2).
Over a portion of the lens, denoted as BL in FIG. 14, the radius of
the curvature of the lens will be transitioning, or blending, from
R1 to R2. This blending will take place over only a small portion
of the lens, and is defined by a succession of, for example, three
or four radii of increasing magnitudes between R1 and R2. Thus, the
actual radius of curvature at any given point in portion BL will be
between R1 and R2 and will change over a small portion of the lens.
The aspherical lens 105 is described as being defined by only two
principal radii (R1 and R2) for purposes of clarity of description
so that the invention is not obscured. However, the present
invention is not limited to an aspherical lens with only two
principal radii. The invention could be practiced with a lens
having more than two such radii, though at a greater cost and
complexity of manufacture.
Referring now to FIG. 15, aspherical lens 105 and prismatic screen
103, along with center axis O-O1 are shown. Here, viewing points A'
and B' are shown at distances FD and CD from the lens,
respectively. In one embodiment, the far distance (FD) center axis
viewing point is 9 feet and the close distance (CD) center axis
viewing point is 3 feet. By this it is meant that the dimensions of
the lens are chosen such that a viewer a distance FD from the lens
can clearly view the image solely through portion S1 of lens 105,
as can a viewer at distance CD from the lens. Determining exactly
what lens dimensions are necessary to achieve this will depend on
the characteristics of the specific device being used, such as
diameter and magnification of lens, and is well within the
competence of the ordinarily skilled artisan. As can be seen from
the Figure, viewing angle <A' at point A' and viewing angle
<B' at point B' are such that the image on the screen is viewed
substantially through the center section S1 of the lens, defined by
radius R1. Thus, little or no image distortion is perceived by the
viewer.
Referring now to FIG. 16, aspherical lens 105 and prismatic screen
103, along with center axis O-O1 are shown. Here, however, viewing
point C', which is at distance CD from the lens 105 and shifted a
distance S to the left of center axis O-O1, is depicted. As shown,
light beams along path L6 pass through center section S1, defined
by radius R1, of the lens and form angle <L6 upon exiting. Light
beams along path L5, however, pass through side section S2, defined
by radius R2, and form angle <L5 upon exiting.
As can be seen by shaded area X, the angle <L5 formed by using
the aspherical lens is less than that angle would have been had a
spherical lens defined only by radius R1 been used. Thus, the
differences between angles <L5 and <L6 are diminished as are
the differences between the magnifications of light along paths L5
and L6 thereby minimizing or removing image distortion caused by
varying magnifications.
FIG. 17 illustrates the aspherical lens 105, screen 103 and center
axis O-O1. FIG. 17 also illustrates interocular distance O.D. at
points A', B' and C'. That is, when designing an aspherical lens to
be used with the present invention, one must take into account the
interocular distance between the eyes of the viewer when choosing
the dimensions of the lens so that the image being viewed is not
seen through one section of the lens (e.g., S1) by one eye and
through another section of the lens (e.g., S2) by the other eye,
thereby causing distortion of the image. Such a situation is shown
in FIG. 17a with respect to viewing point A'. There, the light
along path L1 passes through portion S1 of lens 105 and is seen by
the viewer's right eye at point A.sub.R '. The light along path L2
passes through portion S2 of lens 105 and is seen by the viewer's
left eye at point A.sub.L '. This may cause the viewer to perceive
a distorted image. In order to avoid this situation, the two-point
eye viewing distance should be 20% of the lens diameter.
FIG. 18 illustrates another advantage of the use of an aspherical
lens in the apparatus of the present invention. FIG. 18 again shows
aspherical lens 105 and prismatic screen 103, along with center
axis O-O1. Had a spherical lens, defined solely by radius R1, been
used, the lens would have been of diameter D and thickness LSC1. An
aspherical lens, defined by radii R1 and R2 where R2 is greater
than R1, has a diameter of D', even though only diameter D is
necessary. This permits use of lens of lesser thickness. That is,
an aspherical lens defined by radii R1 and R2 where R2 is greater
than R1 need only be of thickness LSC2 to achieve diameter D. This
center thickness reduction results in a lens weight reduction,
making the device more convenient.
FIG. 19 illustrates a side view of the apparatus of the present
invention using the aspherical lens 105 and comprising video
monitor 100, video monitor screen 101, prismatic screen housing
102, prismatic screen 103 and aspherical lens 105. FIG. 19 also
illustrates center axis O-O1 and three viewing points, O, OT and
OB, each a distance OD from the lens. Viewing point O is on the
center axis O-O1, while point OT is above the center axis and point
OB is below it.
Similar to the situation described above where the viewing point is
displaced orizontally from the center axis of the device, FIG. 19
illustrates how use of an aspherical lens in the present invention
can minimize or remove image distortion when the viewing point is
displaced vertically from the center axis. Specifically, light
beams along path L7 and L8 will pass through different sections (S1
and S2, respectively) of aspherical lens 105, just as light beams
along paths L11 and L12 will pass through different sections (S1
and S2, respectively) of lens 105. Just as described above, use of
an aspherical lens defined by multiple radii will minimize or
remove image distortion for viewers at point OT and OB. FIG. 19
also illustrates how light beams along paths L9 and L10 will pass
through the same, center section, S1, of lens 105, thus not
experiencing distortion.
FIG. 20 shows one example of how the present invention can be used
in the context of a computer monitor. The system is used most
advantageously by disposing the prismatic screen and lens at close
distance from the computer screen by keeping the optical housing
dimensions as small as possible and extending the housing from the
front of the computer monitor screen at a small distance. For
example, FIG. 20 shows a conventional CRT display combined with
aspherical lens ASPL, which is similar to lens 105 described above,
and prismatic screen PRS. In this example, the lens and screen are
placed at a distance of 3 inches in front of the computer screen
CS, though distances as great at 12 inches, and perhaps more, could
be utilized. Computer screen CS is housed in computer housing CH,
which also houses the CRT and associated circuitry (not shown) of
the conventional computer display. Such circuitry is well known in
the art and will not be further described here.
In the example shown in FIG. 20, image a is generated by the CRT
within housing CH in a conventional manner and is transmitted along
axis O-O1. The image can be seen from many different viewing
points, including the point designated VE shown positioned above
the top edge of the computer's screen and inclined at an angle of
30 degrees. Note that different viewing angles are possible by
tilting the computer on its base SB. In the example shown,
prismatic screen PRS and aspherical lens ASPL compensate for the
looking down viewing angle in the manner described above with
respect to FIG. 19.
FIG. 21 shows an aspherical lens ASPL constructed of 50 or more
radii that blend one into the other, as described above. The radius
"A" changes into radius "B" from the center of the lens to its
edge, with each intermediate radius being measured from a different
one of the steps S shown. When the invention is used in the
computer monitor context, radius "B" is advantageously chosen to be
approximately 10% to 40% longer than radius "A" due to the desire
to make the system as compact and lightweight as possible.
FIG. 22 shows the aspherical lens ASPL magnifying computer image S1
so that it appears as virtual curved image S2. Curving the image S1
into S2 separates the images focus from convergence. Combined with
the effects of the prismatic screen PRS, described above, this
allows a viewer to perceive computer image depth cues with much
greater clarity. The aspherical lens in this example is designed to
magnify the computer image 25% or more with no distortion. The
prismatic screen PRS reduces the scanning lines, or the pixel
elements of the computer image, and enhances the resolution of the
image, which helps to eliminate eyestrain. Thus, images are not
only magnified but contain more detail.
A method of making an aspherical lens of the above-described type,
hereafter referred to as a stepped aspherical lens SASPL, will now
be described with reference to FIGS. 29-36. First, a material from
which the stepped aspherical lens SASPL is to be manufactured is
formed into a block using a mold. Exemplary materials for forming
the stepped aspherical lens SASPL may include, but are not limited
to, BK7 glass (having a refraction index of 1.5163) and SK16 glass
which has a higher refraction index of 1.6204. However, it is
preferable and may be advantageous to use high-purity acrylic or
polycarbonate plastic materials having a relatively high index of
refraction.
In one embodiment, a vertical mold M, having a glass lining (not
shown) to minimize contamination, is preferably used to form a
block B, as illustrated by FIG. 29. A selected material is poured
into the mold M and allowed to set from approximately 20-50 days,
depending on the material. This step allows for any impurities to
settle to the bottom of the mold M. The block B is then removed
from the mold M and cut according to the dimensions of a video
image screen with which the stepped aspherical lens SASPL is to be
used.
Referring next to FIG. 30, the block B is then secured to a table T
for milling by a cutting tool. While illustrated in a vertical
position, the block B may alternatively be milled horizontally or
otherwise. The table T is preferably a computer numeric control
(CNC) table, and the tool a CNC cutting tool CT controlled by a CNC
milling machine (not shown). As will be appreciated by those
skilled in the art, the CNC milling machine may be programmed as
desired to carry out cutting of each of a plurality of radii steps
RS to be cut in the surface of the block B, thereby forming a
stepped aspherical lens SASPL, as hereinafter described.
In the exemplary embodiment, the stepped aspherical lens SASPL will
have 50 radii steps RS cut into the surface thereof, as indicated
by each `x` in FIG. 31. The radii steps are then cut by the CNC
cutting tool CT of the CNC milling machine, as seen in FIG. 32. As
the radii steps RS may be cut directly into block B after cutting
the same to a desired size, it is not necessary that the block B
first be cut into a shape of a spherical lens. Alternatively, as
suggested by FIG. 31, the radii steps RS may be cut into a
previously-formed lens.
As can be better seen in FIG. 33, the CNC milling machine is
preferably programmed to cut the radii steps RS such that the
stepped aspherical lens SASPL, while termed aspherical, will
possess pseudo-spherical qualities as well. As indicated by a
dotted line 330, the radii steps RS, cut into the surface of the
stepped aspherical lens SASPL along a predefined curved path, will
further define a spherical surface having a radius Rs. This
pseudo-spherical quality will persist upon a polishing of the
steps, discussed below.
Concurrently, the stepped aspherical lens SASPL will possess an
aspherical quality resulting from the radii steps RS cut into the
surface thereof. Once the plurality of radii steps RS have been cut
into the surface of the stepped aspherical lens SASPL, the steps
are then polished, rounding them and blending the radii steps RS
together such that the individual radii steps RS are no longer
visible. The polishing is preferably achieved on a large, 40 inches
for example, polishing machine, with the stepped aspherical lens
SASPL preferably in a horizontal position, as seen in FIG. 35. The
polishing tool PT preferably uses an aluminum oxide polishing disc
having approximately a 0.5 micron surface, but may alternatively
use any suitable polishing implement. Polishing the individual
radii steps RS reduces them to curved portions. As discussed above
with reference to FIG. 21, these curved portions have gradually
increasing radii which are encountered with travel from a center of
the stepped aspherical lens SASPL to its edge. These curved
portions of varying radii provide the aspherical quality of the
stepped aspherical lens.Referring again to FIG. 34, this SASPL
aspherical quality, in conjunction with the pseudo-spherical
quality, leads to a separation of the focus and convergence
features of a flat image, as perceived by the human brain, leading
to enhanced perception of depth cues from the flat image, as
previously discussed in detail.
Referring to FIG. 34, a radius Rs of the spherical nature of the
stepped aspherical lens SASPL is illustrated. Also shown is a
radius Ra of one of the plurality of steps that define the
aspherical nature of the stepped aspherical lens SASPL
While the radii steps RS are illustrated as being cut and polished
in a single plane in FIG. 30, it should be recognized that the
radii steps RS are formed about a full surface of the stepped
aspherical lens SASPL, as can better be seen by reference to FIG.
33.
FIG. 23 shows the prismatic screen and aspherical lens placed in
front of the computer's monitor screen. It has been discovered that
these elements work as a UV shield, stopping UV radiation which is
harmful for the viewers eyes. This shield also contributes to the
elimination of eyestrain. The light beam OL from the computer's
screen CS, passing through the rear window RW, the prismatic screen
PRS, the aspherical lens AL and the front window FW and is UV
radiation free, before reaching the viewers eyes.
The system of the present invention can be used in conjunction with
all types of computer monitors, including digital high definition
and flat liquid crystal models. FIG. 24, for example, shows the
liquid crystal screen LQS, framed in the flat computer screen
housing FR, without the rear cone shaped tube, which is typical for
regular computer screens. The computer housing DCH attached to the
liquid crystal screen LQS is designed to be narrow and to fit the
flat liquid crystal screen. The liquid crystal computer screen is
characterized with better contrast of the image and better image
resolution. The computer screen system of the present invention
raises the liquid crystal image to a higher quality level, where
the image appears in depth, is magnified and has higher image
resolution.
Referring now to FIG. 25, there is shown an embodiment 1000 of the
endoscope of the present invention. Endoscope 1000 consists of tube
portion 1004, sometimes referred to as a "guide." Tube 1004 is
formed to be hollow in that it has a passageway running
longitudinally down its length. The passageway includes a
sub-passage or smaller tube referred to as the "working channel,"
described in more detail below. Tube portion 1004 may be a rigid
steel tube roughly 30 cm long having an outer diameter of
approximately 1.2 mm. For some procedures, it is more appropriate
to have a shorter rigid guide, such as one approximately 10 cm
long. Tube portion 1004 may alternatively be a flexible tube made
of flexible plastic, or some other suitable material, and having a
length of approximately 110 cm. This longer, flexible tube is
useful in procedures requiring insertion into, for example, blood
vessels of the body. The various guides are formed to be
interchangeable on endoscope 1000 by unscrewing one guide from hub
1001 and screwing in another.
Endoscope 1000 also includes a hub portion 1001 coupled to a tube
portion 1002, and instrument port 1003. Portions 1001 and 1002 and
port 1003 can be made of metal or plastic, or some other suitable
material, as is known in the art. Each includes a longitudinally
formed hollow passageway down its length. Through the hub this
passageway, or biopsy channel, is coupled to the working channel of
the endoscope. These portions together allow the physician to
utilize, for example, a biopsy tube, described in more detail
below, inserted through the biopsy channel and the working channel
of endoscope 1000 in order to perform various medical procedures,
some of which are described in further detail below.
Although not necessary for every embodiment of the invention, FIG.
25 shows endoscope 1000 as including tube portion 1005 coupled to
mini-hub 1001a, which is coupled to tube portion 1002, and to
irrigation port 1006. In one embodiment, tube portion 1005 is
approximately 1 foot long. Portion 1005, mini-hub 1001a and
irrigation port 1006 may also be made from any suitable material,
such as plastic or metal, though forming them of a flexible
material, such as a flexible plastic, makes them somewhat easier to
work with. Portion 1005, mini-hub 1001a and irrigation port 1006
are formed such that a passageway runs down their middle, referred
to here as the "irrigation channel," which passageway is coupled to
the biopsy channel of tube portion 1002 and, thereby, to the
working channel of endoscope 1000. (By proper formation of the hub
1001, the irrigation channel could also be coupled directly to the
working channel.)
These portions of endoscope 1000 allow the physician to irrigate
the area of the body being treated. For example, through the
irrigation channel liquids or air may be injected into the working
channel and thereby to the area of the body being treated. Such
liquids can include water, saline, anesthetics, or antiseptics. The
injection can occur through the operation of a syringe or other
similar instrument coupled to irrigation port 1006. Moreover, the
irrigation channel can also be used as a port through which a
laser, such as an Eximer laser, could be utilized. In that
situation, the laser is inserted through the irrigation channel and
into the working channel until it reaches the area of interest
internal to the patient. The laser can then be used, for example,
as a means for clearing a blocked passageway.
Although again not necessary for every embodiment, FIG. 25 also
shows endoscope 1000 as including tube portion 1007 coupled between
hub 1001 and video port 1008. As one skilled in the art will
appreciate, the video port 1008 may be any suitable video coupler,
and will preferably include magnification means. Tube portion 1007,
in one embodiment, is approximately 2.5 feet long and is formed
most advantageously with some flexible material, such as a flexible
plastic, so that it can be easily connected to video equipment and
the like. Tube 1007 and video port 1008 are formed such that they
include a passageway in their interior capable of holding numerous
fiber optic strands. Such strands run from video port 1008, through
tube portion 1007 into hub 1001. The strands run through hub 1001
into the inner passageway of tube portion 1004, though outside of
the working channel, as described in more detail below. These
strands provide both a light source to the area of interest and a
video source to the video port, allowing the physician to see an
image of the area of interest while treatment is occurring. Video
port 1008 is therefore formed such that it includes a light source
connector 1009 and can be coupled to a video camera, monitor and
raster screen, as described in more detail below. As a result of
the improved magnification and viewing qualities achieved using
aspherical lenses of the type discussed above, it has been found
that a video coupler having a lower magnification than in
conventional endoscope systems may be used.
A cross-sectional view of a stainless steel guide 1004, as seen
from viewpoint A--A on FIG. 25, is shown in detail in FIG. 26. In
FIG. 26, the rigid, steel tube option is depicted, although the
figure could just as readily depict the flexible tube option. More
specifically, FIG. 26 shows tube portion 1004, which contains
working channel 2001, a plurality of optical light fibers 2002 and
lens 2003. Guide 1004 has an outer diameter of approximately 1.2
mm. Working channel 2001 has an outer diameter of approximately
0.35 mm and an inner diameter of approximately 0.25 mm. Tubing for
such a channel can be obtained from, for example, Solos Endoscopy
Co. of Braintree, Me.
The use of a working channel 2001 having a reduced working channel
outer diameter, such as 0.35 mm allows for a corresponding increase
in the number of optical or light fibers 2002 and/or an increase in
the size of the lens 2003 in the image fiber optical channel (see
e.g., FIG. 26). In addition, because of the decrease in overall
size of the endoscopes of the present invention, countless medical
procedures can be performed in a less invasive and less traumatic
manner than was previously known. For example, in many cases, ducts
may be utilized as entry points to a body, as opposed to a surgical
incision. Moreover, ductules, such as those of the female breast,
which previously were inaccessible due to the size of conventional
endoscopic devices, can now be analyzed and diagnosed for diseases,
such as cancer, well before such diagnoses would be available with
conventional systems.
In the embodiment shown in this figure there are 16 optical fibers
running down the length of guide 1004, each having a diameter of
approximately 0.125 mm. These fibers act to provide light to the
area of interest, although a different number of fibers and/or
fibers of different diameters may also be used. Lens 2003 also runs
longitudinally down the inner passage of guide 1004 and has a
diameter of 0.35 mm.
Referring now to FIG. 27, there is shown a sectional elevation of a
biopsy tube 3000 to be used with the endoscope of the present
invention. The biopsy tube 3000 includes tube portion 3001, which
includes a hollow passageway down its length, coupled to syringe
3002, or some other similar instrument, and having an end portion
3003. The tube has an outer diameter of approximately 0.135 mm
which allows it to be inserted into the working channel of guide
1004 of endoscope 1000, as shown in FIG. 3A.
In one embodiment, end portion 3003 does not include a scraper or
biopsy brush for the extraction of biopsy cells, although in other
embodiments it could. Rather, the distal end of the biopsy tube has
no brush or medical instrument whatsoever attached and is more like
the end of a tube or needle. Because the tube is of such a small
outer diameter, the physician can manipulate the biopsy tube from
the proximal end in order to scrape cells free of the tissue. The
physician can then irrigate the location by ejecting water under
pressure through the irrigation channel through the operation of
syringe 3002. This causes the water injected into the patient to
mix with the scraped biopsy cells. Such water and cells can be
drawn into the biopsy tube 3000 by withdrawing the plunger of the
syringe 3002. Once the endoscope is removed from the patient's
body, the plunger of syringe 3002 can be pushed back in and the
biopsy cells disgorged onto a slide or into a transmission medium
for later testing.
Biopsy tube 3000 can be made of stainless steel, flexible plastic,
or some other suitable material, depending on the guide with which
it will be used. A biopsy tube suitable for use in the present
invention may be obtained from United Machines, Inc. of Bohemia,
N.Y.
In further exemplary embodiments, it will be preferable to utilize
a biopsy tube 3000, or other instrument to be inserted into an
endoscope working channel, such as a scraper or cytology instrument
having a roughened end portion. Particularly for use in a
relatively small working channel, such as the 0.35 mm channel as
discussed above or smaller, a composition of the cytology
instrument will be important. In one embodiment, a cytology
instrument is contemplated which has a 0.25-0.30 mm diameter for
use in a 0.33-0.35 mm working channel. Because of the relatively
small proportions, the cytology instrument must be formed of a
material having sufficient strength to allow effective scraping and
cell removal. Since the end portion 3000 will be used within the
body, the end portion 3000 is further preferably formed of, or at
least coated by, a suitable biocompatible material.
One material that meets these requirements is Nitinol (NiTi), an
alloy of titanium. It is contemplated that forming further alloys
by combining Nitinol with other elements or compounds may lead to
suitable materials as well. Nitinol has been found to exhibit
favorable strength and biocompatibility characteristics in numerous
surgical applications. For example, Nitinol enjoys a high tensile
strength and resistance to lateral deformation, as well as
resilience to an environment of the human body, such that a device
formed thereof can be used repeatedly without degradation.
Importantly, Nitinol has further been classified as biologically
inactive, indicating that internal use of Nitinol elicits a
minimal, if any, negative response from the human body. Further
information regarding the biocompatibility of Nitinol may be
obtained by reference to the following dissertation which is hereby
incorporated herein by reference in its entirety: Ryhanen, Jorma,
"Biocompatibility Evaluation of Nickel-Titanium Shape Memory Metal
Alloy," presented at the University Hospital of Oulu, Finland, May
7, 1999 (presently available at
http://herkules.oulu.fi/issn03553221/).
A cytology instrument of this embodiment advantageously has a
working end adapted for any of a variety of biopsy functions, such
as scraping. Therefore, the working end may be roughened or
otherwise made abrasive for this purpose.
A roughened working end may be formed in a variety of ways. For
example, a laser energy source may be directed at a Nitinol
instrument, thereby removing an oxide layer at the surface. This
will leave behind an abrasive surface that is suitable for
scraping. Alternatively, the oxide layer may be removed by
sandblasting, which will also leave a roughened surface.
In another embodiment, a Nitinol surface may be roughened to form
an abrasive surface by stone grinding, such as with a stone wheel.
The degree of abrasiveness may be controlled by varying an amount
of stone grinding. Alternatively, a tool and die can be used to
impart a controllable amount of roughness to a Nitinol surface. In
this method, the tool and die are used to score the surface
creating a desired abrasiveness.
A method of using a Nitinol cytology instrument to retrieve biopsy
cells or other bodily materials will now be described. As discussed
above with respect to FIGS. 26 and 27, the endoscope 1000 is first
used to locate an area of the body to be biopsied. The area may be
a cell, tissue or other abnormality, such as a papilloma or other
tumor, or alternatively an area of normal, healthy cells, such as
in preventative and/or diagnostic procedures.
The Nitinol cytology instrument will then be inserted through the
working channel 1003, and manipulated with the visual assistance of
the endoscope 1000 to scrape a portion of the area, perhaps a
number of cells, a sample of lining, etc., from the area to be
biopsied or studied. A syringe or other means is used to inject a
fluid, such as saline solution, through the irrigation channel
1005, such that the fluid and biopsied material mix. Alternatively,
the fluid may be injected prior to the scraping. Next, to remove
the biopsied material, it is preferable in this embodiment to
aspirate the injected fluid and biopsied material through the
working channel following removal of the Nitinol cytology
instrument. Once the mixture of biopsied material and fluid has
been aspirated, samples thereof may be tested in any of a variety
of ways, or placed on a slide for viewing under a microscope.
It is also an advantageous feature of the present invention that,
because the above-described procedure is carried out
endoscopically, as compared to a biopsy via an open incision for
example, biopsied materials, such as papillomas, have a reduced
tendency to migrate within the body prior to aspiration. This
feature is important not only in obtaining a complete sample, but
also in preventing contamination of other areas of the body with
biopsied material. For example, the spread of tumor cells within
the body, particularly if cancerous, can be highly detrimental to a
patient.
FIG. 28 depicts endoscope 1000 used in conjunction with a video
monitor and prismatic screen as described above. For example, in
FIG. 28 the video port 1008 is coupled to a video camera 4001, the
output of which is coupled to video monitor 4002 having as an
attachment prismatic screen 4003. Prismatic screen may also include
an optical element, such as a spherical or aspherical lens or other
device, as described above.
Video camera 4001 may be of many different commercially available
models, although CCD cameras are particularly useful in this type
of application. Specifically, a Panasonic GS9900-NTSC medical video
endoscopy camera, from Matsushita Electric Corporation of America,
has been found to be useful. Moreover, it has been found that in
such a camera a 1/4 inch CCD chip is more advantageous than a 1/2
inch CCD chip, because it provides an image with smaller pixels.
Such chips are included in CCD cameras and also are commercially
available from many sources such as, for example, the Sony
Corporation of America. Video monitor 4002 may be any of a number
of commercially available video monitors.
Referring now to FIGS. 37 and 38, there are shown a conventional
endoscope employing a 1/2 inch CCD chip 37b and a preferred
embodiment of the present invention employing a 1/4 inch video CCD
chip 38b, respectively. As can be seen by comparing FIGS. 37 and
38, the present invention provides for a closer focus distance X.
Such a shortened focus distance is achieved by refocusing the
coupler 37c to a shorter optical distance and by reducing the size
of the CCD chip to 1/4". Exemplary focus distances are from about
1.0 to about 2.0 mm as compared to about 4.0 mm for a 3.0 diameter
conventional endoscope. Such short focal lengths are advantageous
for performing medical procedures in, for example, but not limited
to, small ductules, like those present in the human breast and
other areas of the human body as described herein.
These shortened focus distances are also achieved by reconfiguring
the video camera housing and coupling the video CCD chip at a
closer distance (depicted as Y in FIGS. 37 and 38) to the coupler
37c. The video camera is optically redesigned with a new housing
and shorter distance bracket than conventional systems which allows
the distance between the video chip 38b and the front of the video
camera to be much shorter than conventional systems (see Z in FIGS.
37 and 38). It should also be apparent to one skilled in the art
that refocusing lens 37a can be any suitable lens, for example, but
not limited to, a spherical, drum, aspherical, or stepped
aspherical lens, as described herein.
The present invention allows the image magnification to be
maintained at the prior level of much larger endoscopic systems
without degradations in image quality which are inherent in
conventional microendoscopic systems. The same number of scanning
lines can be achieved with shorter focal lengths and larger depths
of field (e.g., about 50% larger for a focus distance of about 1 to
about 2 mm) by dividing each scanning line into three or more
lines, thereby increasing projected image quality by reducing the
visibility of the scanning lines. Larger depths of field are
achieved because of the shortened optical focal length of the
coupler as shown in FIG. 39. As a result, smaller, less visible
scanning lines are present thereby facilitating numerous medical
procedures which were previously unattainable given the image and
quality limitations of conventional microendoscopic systems.
It is not necessary to include a prismatic screen to use the
endoscope of the present invention. However, the use of such a
screen is advantageous because, as described above, the screen
provides an image with increased clarity and perception of depth by
causing the brain of the viewer to interpret depth cues present in
the image. This increased perception of depth is particularly
advantageous in medical procedures like those that employ
endoscopes because of the small dimensions involved and the limited
lighting available in the interior of a patient's body. Moreover,
because the fiber optic elements of any endoscope are necessarily
small, the image generated by them is also small, limiting its
usefulness to the physician and its practicality during the
procedure. The prismatic screen described in the patents and
application above, when used conjunction with the endoscopic
instrument described above, produces an image anywhere from 25% to
100% larger than use of the instrument without the screen. Thus,
the endoscope of the present invention coupled with the prismatic
screen of the above referenced patents and patent application
permit the physician to perform the biopsy, or other procedure,
while actually viewing the progress and operation of the instrument
and to do so in a much more advantageous manner.
Operation of endoscope 1000 will now be described briefly in order
better to explain various uses of the invention in some situations.
Generally speaking, endoscope 1000, using either the flexible or
rigid guides 1004, is inserted into an orifice or incision in the
patient's body. The physician can view the areas of the body
through which the endoscope passes on its way to the area of
interest and can view the area of interest once it is reached by
watching the screen 4003 attached to video monitor 4002. Once at
the appropriate place in the patient's body, the physician can
manipulate the biopsy tube 3001 in order to retrieves cells from
that area or perform some other medical procedure. For example, the
physician can inject water into the area of interest through the
working channel using a syringe coupled to the biopsy tube. He can
then aspirate the water and sample cells through the operation of
the syringe. The cells are then retrieved with the water, through
the working channel, poured into a sterilized plastic container,
for example, and taken to pathology for diagnostic testing.
Occasionally the lens of endoscope 1000 may need to be cleared of
blood and cell particles as a procedure is being performed. The
irrigation channel and the working channel may be used in
performing this function by, first, applying a liquid under
pressure through the use of a syringe attached to the irrigation
port. This has the effect of both widening the viewing area and
clearing the viewing area of blood. However, it is important to
apply the fluid using a pressure higher than that of the blood.
Second, because liquids will often become quickly colored with
blood, air pressure is applied through the working channel by a
syringe coupled to the irrigation port. This creates a small cavity
around the end of the endoscope and pushes the fluids in the
patient's body out of the viewing area. This, consequently, clears
the way for the light emitted from the light source optical fibers
and for the resulting light entering the lens, thereby creating a
much clearer image for the physician.
The present invention can be used in many different specialized
procedures. For example, the endoscope of the present invention can
be used in a breast duct diagnostic procedure whereby the guide is
inserted through the dilated nipple of the breast and the area of
interest is viewed on the screen. A biopsy may be performed if
necessary. Thus, the present invention allows a non-invasive
procedure useful in detecting breast cancer through direct
visualization by the treating physician.
The present invention may also be used in techniques similar to
angiograms and angioplasty, whereby the endoscope 1000 utilizing a
flexible guide is inserted into an artery. The treating physician
can see the inside of the artery on the screen and can determine
the extent and type, if any, of blockage in the artery. This
technique can also be used with respect to smaller veins and
arteries that carry blood to and from much more difficult parts of
the body to reach, such as the lungs, neck and chest.
Glaucoma investigation and other ocular procedures can also be
accomplished with the present invention, most usefully using a
shorter, rigid guide. Such procedures include inserting the guide
of the endoscope into the tear duct of the eye, viewing its
interior on the screen and performing a medical procedure, such as
aspiration, for example, or clearing of a blocked passageway
through the utilization of an Eximer laser.
In addition, the present invention can be used to traverse the
optical nerve such that the alignment between the optical nerve and
the brain can be checked prior to, and following, for example, a
corneal transplant or other ocular transplant or surgery. In
addition to alignment between the optical nerve and the brain, the
present invention allows for identification and treatment of other
abnormalities that might exist within the optical nerve that were
previously undetectable using conventional systems.
Indeed, a particularly advantageous use of the present invention is
in the treatment of cancer in various parts of the body. Cancer is
generally treatable in three ways: surgery, radiation and
chemotherapy. Surgery and radiation, of course, have risks and
disadvantages well known to those of skill in the art. Chemotherapy
also can be particularly disadvantageous as, for example, when the
drugs involved cause sickness to the patient when they enter the
blood stream. One advantage of the present invention is that, due
to its size and the quality of image obtainable, the physician can
inject liquids directly into a cancerous tumor, minimizing the
collateral damage or exposure to chemotherapeutic chemicals to
other portions of the body.
Because of the microscopic size of the endoscope of the present
invention, papillomas or other cancerous growths can be diagnosed
well in advance of when they were able to be detected and treated
using conventional open breast surgeries or the like. For example,
using the system of the present invention, the endoscope can be
used to traverse a breast ductule up to a papilloma or other
abnormality. A laser, such as an Eximer laser, or other suitable
device can then be inserted into the small working channel of the
endoscope and positioned adjacent the abnormality. In this fashion,
the laser can be used to burn or otherwise break up the abnormality
whereupon it can be removed from the body. Through use of the
present invention, microprocedures such as those described herein
provide an invaluable ability to both view cancerous growths in
their infancy and provide a means by which to remove the air
cancerous growths before they are allowed to spread to other parts
of the body. Indeed, such procedures can be accomplished without
the more invasive techniques of open breast surgeries and the
like.
Further, the present invention is useful in the diagnosis and
treatment of prostate cancer that often requires surgery or an
extremely invasive endoscopic procedure through the penis or anus.
The endoscopic system of the present invention permits a much less
invasive procedure and allows the physician to visualize, by seeing
on the screen, exactly what is happening as it happens.
This invention is also particularly useful in pediatric
applications, such as a drainage of the lacrimal sinus of an infant
in order to aspirate any pools of mucus that have built up in the
underdeveloped sinus of the child, thereby halting any developing
infection.
Indeed, procedures in which physicians must invade any cavity of
the body whether in children or adults, and in which physicians
have been visually limited in the past, may be performed with the
present invention in a much less invasive manner and with the
physician able to see exactly what he or she is doing. Such
procedures include, for example, laryngeal and esophagus related
procedures, peritoneal and abdominal cavity procedures, obstetrics
and gynecological procedures, sigmoid-colon procedures, parotid
gland procedures, oral surgery, including root canals, spinal cord
procedures, procedures directed to the lymph nodes, small joint
procedures and even medical procedures on animals.
The principles, embodiments and modes of operation of the present
invention have been described in the foregoing specification. The
invention that is sought to be protected herein, however, is not to
be considered as limited to the particular forms disclosed, since
these are to be regarded as illustrative rather than restrictive.
Variations and changes may be made by those skilled in the art
without departing from the spirit and scope of the invention. For
example, the present invention is not limited to the particular
dimensions or uses described, except as explicitly defined in the
claims.
* * * * *
References