U.S. patent application number 13/232151 was filed with the patent office on 2012-03-22 for device and method for wide-field and high resolution imaging of tissue.
This patent application is currently assigned to The General Hospital Corporation. Invention is credited to Richard R. Anderson, Robert H. Webb, Anna N. Yaroslavsky.
Application Number | 20120071764 13/232151 |
Document ID | / |
Family ID | 38895166 |
Filed Date | 2012-03-22 |
United States Patent
Application |
20120071764 |
Kind Code |
A1 |
Yaroslavsky; Anna N. ; et
al. |
March 22, 2012 |
DEVICE AND METHOD FOR WIDE-FIELD AND HIGH RESOLUTION IMAGING OF
TISSUE
Abstract
A device for wide-field and high resolution imaging of an object
surface includes first and second imaging modalities, a lens
associated with the second imaging modality. The first imaging
modality is high resolution with a first observation line. The
second imaging modality is arranged in an image plane at a first
angle with respect to an object plane and has a second observation
line and a wider imaging field than the first imaging modality. The
lens associated with the second imaging modality is arranged in a
lens plane at a second angle with respect to the object plane,
where the second angle being equal to about one-half of the first
angle. The first and second imaging modalities are mutually
arranged such that the first and second optical axes intersect at a
point on the object plane.
Inventors: |
Yaroslavsky; Anna N.; (N.
Andover, MA) ; Webb; Robert H.; (Lincoln, MA)
; Anderson; Richard R.; (Boston, MA) |
Assignee: |
The General Hospital
Corporation
Boston
MA
|
Family ID: |
38895166 |
Appl. No.: |
13/232151 |
Filed: |
September 14, 2011 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
11823610 |
Jun 28, 2007 |
8045263 |
|
|
13232151 |
|
|
|
|
60818200 |
Jun 30, 2006 |
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Current U.S.
Class: |
600/476 ; 348/36;
348/E5.024 |
Current CPC
Class: |
A61B 5/0071 20130101;
A61B 5/0068 20130101; A61B 5/444 20130101; G02B 21/0024
20130101 |
Class at
Publication: |
600/476 ; 348/36;
348/E05.024 |
International
Class: |
A61B 6/00 20060101
A61B006/00; H04N 7/00 20110101 H04N007/00 |
Claims
1-17. (canceled)
18. A system for providing wide-field and high resolution images,
comprising: a first imaging modality having high-resolution imaging
means; a second imaging modality including an image sensor arranged
in an image plane at a first angle with respect to an object plane,
having a wider imaging field than the first imaging modality; and a
computer system operatively associated with the first and second
imaging modalities, the computer system comprising a processor and
executable code being adapted and configured to: capture a first
image by way of the second imaging modality; receive instructions
to image with the first imaging modality, a selected region of the
first image; capture a second image of the selected region, via the
first imaging modality, in accordance with the instructions.
19. The system of claim 18, wherein the system further comprises:
an objective lens with a first observation line associated with the
first imaging modality, the second imaging modality having a second
observation line; and a lens associated with the second imaging
modality, arranged in a lens plane at a second angle with respect
to the object plane, the second angle being equal to about one-half
of the first angle, the first and second imaging modalities being
mutually arranged such that the first and second optical axes
intersect at a point on the object plane.
20. A method of wide-field and high resolution imaging of an
object, the method comprising: providing a device having: a first
imaging modality having high-resolution imaging means and a first
observation line; and a second imaging modality including an image
sensor arranged in an image plane at a first angle with respect to
an object plane, the second imaging modality having a second
observation line and a wider imaging field than the first imaging
modality; positioning the first and second imaging modalities in an
imaging region of an object surface of which an image is desired,
such that the first and second optical axes mutually intersect in
the imaging region; illuminating the imaging region via confocal
optics of the first imaging modality; capturing a first image of
the imaging region with the second imaging modality; identifying a
first sub-region of interest within the first image of the imaging
region; capturing a second image of the first sub-region with the
first imaging modality; and analyzing the second image.
21. The method of claim 20, further comprising: identifying a
second sub-region of interest; capturing a third image of the
second sub-region with the first imaging modality; and analyzing
the third image.
22. The method of claim 21, wherein identification of the first and
second sub-regions of interest occur concurrently, prior to
capturing of the second and third images.
23. The method of claim 20, further comprising: illuminating the
imaging region with a first frequency of light while capturing the
first image; and illuminating the sub-region with the first
frequency of light while capturing the second image.
24. The method of claim 23, further comprising: illuminating the
imaging region with a second frequency of light while capturing a
third image of the imaging region; and illuminating the sub-region
with the second frequency of light while capturing a fourth image
of the sub-region.
25. The method of claim 20, further comprising: illuminating the
imaging region with polychromatic light while capturing a fifth
image of the imaging region; and illuminating the sub-region while
capturing a sixth image of the sub-region.
26. The method of claim 20, wherein the first and second images
each include a plurality of images acquired with different imaging
techniques.
27. The method of claim 20, wherein analysis of the second image is
performed to find abnormal cell growth in skin of a patient
28. The method of claim 20, wherein identification of the one or
more sub regions is performed automatically by a computer
system.
29. The method of claim 20, wherein analysis of the second image is
performed automatically by a computer system.
30. A system for providing wide-field and high resolution images,
comprising: a first imaging modality having high-resolution imaging
means; a second imaging modality capable of providing a macroscopic
image having a wider imaging field than the first imaging modality;
and a computer system operatively associated with the first and
second imaging modalities, the computer system comprising a
processor and executable code being adapted and configured to:
receive instructions from a user to capture a macroscopic first
image of an object; capture a first image of the object by way of
the second imaging modality; display the first image for a user to
view; receive input selecting a first region of the first image,
corresponding to a first region of the object, to be imaged with
the first imaging modality; send instructions to adjust the first
imaging modality to a position in which an image of the first
region can be captured; and capture a second image of the first
region, via the first imaging modality.
31. The method of claim 30, wherein the computer system comprises a
processor and executable code are further adapted and configured to
store the first and second captured images, the first and second
captured images being in color.
32. The method of claim 30, wherein the computer system comprises a
processor and executable code are further adapted and configured
to: receive input selecting a second region of the first image,
corresponding to a second region of the object, to be imaged with
the first imaging modality; send instructions to adjust the first
imaging modality to a position in which an image of the second
region can be captured; and capture a third image of the second
region, via the first imaging modality.
33. The method of claim 32, wherein the computer system comprises a
processor and executable code are further adapted and configured
to: receive input selecting a third region of the first image,
corresponding to a third region of the object, to be imaged with
the first imaging modality; send instructions to adjust the first
imaging modality to a position in which an image of the third
region can be captured; and capture a fourth image of the third
region, via the first imaging modality.
Description
CROSS-REFERENCE TO RELATED APPLICATION
[0001] This application is a division of U.S. application Ser. No.
11/823,610, filed Jun. 28, 2007, now U.S. Pat. No. 8,045,263, which
claims priority to U.S. Provisional Patent Application No.
60/818,200 filed Jun. 30, 2006. The entire contents of each of the
aforementioned applications are hereby incorporated herein by this
reference.
BACKGROUND OF THE INVENTION
[0002] This invention was made with Government support under Grant
No. eB002423 awarded by the National Institutes of Health. The
Government has certain rights in the invention.
Field of the Invention
[0003] The present invention relates to a device and method for
wide-field and high resolution imaging. Particularly, the present
invention is directed to a system having wide-field and high
resolution imaging capability.
[0004] The present invention is particularly suitable for imaging
skin cancer, e.g., as a rapid bedside guide to tumor excision. The
invention is useful for providing enhanced imaging of epithelial
tumors, inflammatory disorders, or other pathological conditions,
including nonmelanoma skin cancer. However, the subject device and
method may be used for imaging and analyzing surface, structural,
spectral, functional, fluorescence, Raman, bio-chemical,
polarization and other similar characteristics of any object when
the combination of wide field imaging and high resolution is
required.
Description of Related Art
[0005] Advances in the development of optical imaging modalities
have facilitated efforts to employ these techniques for noninvasive
detection and treatment guidance of different pathological
conditions. In general, the turbidity of tissue creates major
challenges for optical in vivo spectroscopy and imaging. However,
reflectance and fluorescence imaging techniques, like
multi-spectral polarized light macro-imaging and confocal
microscopy are well suited for skin cancer detection and
demarcation. Confocal reflectance microscopy was introduced to the
field of dermatology in the 1990s. Since then, it has been used to
study different skin disorders.
[0006] Confocal microscopy is a technique where the specimen is
pointwise illuminated by a focused beam of light. An image is
recorded by scanning the beam focus through a plane in the
specimen, and the reflected light from the specimen is focused onto
a small detector aperture. The light source, the illuminated spot
and the detector aperture are placed in optically conjugated focal
planes. "Optical sectioning" occurs as out-of-focal-plane
back-scattered light is rejected by a pinhole placed in front of a
detector. Optical sectioning makes it possible to record images of
thin layers within tissue. Confocal microscopy allows imaging
within turbid media with high resolution (lateral resolution of
about 1 .mu.m, and axial resolution (section thickness) of about
3-5 .mu.m), which is comparable to histology. The major
disadvantage of confocal microscopy as a detection and guidance
tool for cancer surgery is its small field of view, which is
typically, up to about 0.3 mm. To examine an entire suspected
cancerous area using confocal microscopy (CM), a sequence of images
must be captured and stitched together. This process takes time and
motion artifacts may distort the resulting image.
[0007] Multi-spectral polarized light imaging (MSPLI) is a simple
and inexpensive technique for skin tumor imaging. The technique
provides the means to differentiate effectively between endogenous
(blood, melanin, etc.) and exogenous (dye) chromophores absorbing
in different spectral domains, and is capable of obtaining
superficial images (at a resolution of about 3-50 .mu.m-lateral,
5-0200 .mu.m-axial in the visible spectral range) of thick tissue
layers. Such imaging is relatively insensitive to small shifts in
the position of the imaged object, and combination of the large
field-of-view and sufficient lateral resolution enables rapid
examination of large surfaces, thus facilitating tumor margin
delineation. However, morphology of individual cells and fine
structures cannot be resolved using MSPLI. Thus, the multi-spectral
polarized light imaging approach can benefit from combination with
a high-resolution technique, such as confocal reflectance
microscopy, which can be used by a pathologist in the cases when
high-resolution images of small suspicious areas are required. Such
combination may become a powerful tool for cancer detection and
demarcation.
SUMMARY OF THE INVENTION
[0008] The purpose and advantages of the present invention will be
set forth in and apparent from the description that follows.
Additional advantages of the invention will be description and
claims hereof, as well as from the appended drawings.
[0009] The present technology relates to a novel device that
combines a wide-field, low-resolution imaging modality and a
high-resolution, narrow-field imaging modality, which preferably
share a common light source and hardware control unit. One
preferred embodiment includes a combination of confocal microscopy
with wide-field CCD (charge-coupled device) imaging. By combining
these two imaging devices, a high resolution wide-field imaging is
effectively achieved. CCD imaging, for example, the technique of
multi-spectral polarized light imaging (MSPLI), enables rapid
inspection of a superficial tissue layer over large surfaces, but
does not provide information on cellular microstructure. Confocal
microscopy (CM) allows imaging within turbid media with resolution
comparable to that of histology, but suffers from a small field of
view. Typically, pathologists use microscopes at low power and high
power, to view the margins of pathology and cell features,
respectively. Therefore, the present technology, which can combine,
for example, MSPLI and CM can guide cancer surgery more rapidly,
and at lower cost than conventional histopathology.
[0010] To achieve these and other advantages and in accordance with
the purpose of the subject technology, as embodied, the subject
technology includes a device for wide-field and high resolution
imaging of an object surface includes first and second imaging
modalities, a lens associated with the second imaging modality. The
first imaging modality has a high resolution imaging means with a
first observation line, such as an optical axis in the event that
the imaging modality is optical. It will be understood that
non-optical imaging modalities can also be used including but not
limited to acoustic (e.g., ultrasonic), terahertz and the like, for
example.
[0011] The second imaging modality is arranged in an image plane at
a first angle with respect to an object plane and has a second
observation line and a wider imaging field than the first imaging
modality. The lens associated with the second imaging modality is
arranged in a lens plane at a second angle with respect to the
object plane, where the second angle being equal to about one-half
of the first angle. The first and second imaging modalities are
mutually arranged such that the first and second optical axes
intersect at a point on the object plane.
[0012] The first imaging modality can include a confocal microscope
including an objective lens, a multi-photon microscope, a
high-resolution CCD imaging device or another high-resolution
imaging device.
[0013] Devices in accordance with the present technology can be
capable of adjusting to a first configuration, in which the second
imaging modality is capable of capturing an image and/or to a
second configuration, in which the first imaging modality is
capable of capturing a high-resolution image. The first imaging
modality can be capable of imaging both an object surface as well
as beneath the object surface. The first and second imaging
modalities can be supported by a supporting structure, such
supporting structure providing rigidity, providing support to the
device components, and/or enabling the device to be moved with
respect to the object surface. The second modality and the lens can
be pivotally supported by the device.
[0014] It is to be understood that both the foregoing general
description and the following detailed description are exemplary
and are intended to provide a non-limiting explanation of the
subject technology.
BRIEF DESCRIPTION OF THE DRAWINGS
[0015] The patent or application file contains at least one drawing
executed in color. Copies of this patent or patent application
publication with a color drawing(s) will be provided by the Office
upon request and payment of the necessary fee.
[0016] The accompanying drawings, which are incorporated in and
constitute part of this specification, are included to illustrate
and provide a further understanding of the method and system of the
invention.
[0017] FIG. 1 is a schematic layout of a multimodal wide-field,
high-resolution imaging system in accordance with the present
technology.
[0018] FIG. 2 is a schematic representation of an optical layout
from box A of FIGS. 1.
[0019] FIG. 3 is a series graphic representations, a-i, of
exemplary image outputs from a system in accordance with the
present technology.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT
[0020] Reference will now be made in detail to the present
preferred embodiments of the invention, an example of which is
illustrated in the accompanying drawings. The method and
corresponding steps of the subject technology will be described in
conjunction with the detailed description of the system.
[0021] For purpose of explanation and illustration, and not
limitation, a view of an exemplary embodiment of a system 100 in
accordance with the present technology is illustrated in FIG. 1.
FIG. 2 illustrates in more detail the optical layout within region
A of FIG. 1.
[0022] The present technology includes both a device and a method
for effectively obtaining high-resolution wide-field optical
imagery, which cannot be achieved with previously known devices or
methods. This is achieved by combining a pair of imaging
modalities: a wide-field relatively low-resolution imaging modality
and a high-resolution, relatively narrow-field imaging modality,
which preferably share a common light source. Either monochromatic
or polychromatic light source can be employed, including, but not
limited to, lasers, LEDs, discharge lamps, incandescent lamps, and
the like. The illumination wavelength can be in the range between
10 nm and 1 mm. The detected radiation can be elastically
scattered, fluorescent, Raman, non-linearly formed (e.g., second
harmonic), or generated as a result of another physical phenomenon
in the imaged object.
[0023] In one preferred embodiment, the wide-field modality is
polarization-enhanced elastic/fluorescent imaging with a CCD
sensor, and the high-resolution modality is confocal microscopy.
Both modes can be controlled by a computer or a similar control
device. In such an arrangement, the user is preferably able to
switch seamlessly between the first and second imaging modalities.
The high-resolution modality can be automatically positioned at the
point of interest selected by the user within the field-of-view of
the wide-field modality, with subsequent image acquisition by the
high-resolution modality from a region near that point.
Alternatively, the point of interest to be imaged with the
high-resolution imaging modality can be automatically selected by a
computer, based on predetermined identifyable characteristics, such
as predetermined surface features.
[0024] FIG. 1 illustrates a schematic of an example embodiment of a
system in accordance with the subject technology. In this exemplary
embodiment, an advantage achieved by combining the macroscopic and
confocal imaging into a single unit with common illumination, image
acquisition, and hardware control, is the ability to rapidly
inspect large surfaces. Based on the analysis of macroscopic
images, if necessary, one can zoom-in and acquire (automatically or
manually), narrow-field, high-resolution confocal images of the
desired regions, such as suspicious parts of a skin lesion of a
patient. The time required for the detection of tumor margins and
small tumor nests is thus dramatically reduced as compared with
existing devices and methods.
[0025] Further, if embodied with automatic positioning capability,
devices in accordance with the subject technology can precisely
automatically center the high-resolution imaging modality, such as
a confocal imaging system, at the area of interest selected by
analyzing an image captured with the wide-field imaging modality.
Accuracy of tissue discrimination will therefore be significantly
improved.
[0026] With reference to the system 100 as depicted in FIG. 1, the
illumination for both macro and confocal imaging is preferably
provided by the same source or sources of light, such as by diode
lasers 111, 112. In general, light of any wavelength in a range
from about 190 nm to about 2600 nm can be used. However, when used
for tumor delineation, lasers 111, 112 emitting linearly polarized
light at the wavelengths of 650 nm and 750 nm, respectively can be
used. Light having a wavelength of 650 nm lies within the
absorption band of Methylene Blue (MB) contrast agent, and light of
wavelength of 750 nm is a reference wavelength outside the
absorption band of MB. In the confocal optical subsystem 110 of
system 100, a polarizing beam splitter 119 further increases the
degree of linear polarization of the light incident on the tissue.
For simultaneous registration of the reflectance and fluorescence
images, a 90/10 non-polarizing beam splitter 121 is installed after
the polarizing beam splitter 119. Beam stops 120 and 122 are
provided, as needed. As set forth above, the confocal optical
subsystem 110 can instead be replaced any suitable high-resolution
imaging device. Such devices can include, but are not limited to a
multi-photon microscope or a high-resolution CCD device, for
example.
[0027] In the embodiment of FIG. 1, the optical components are
mounted in a supporting structure 160. The lens 217 and the CCD
device 240, among other components may be mounted in the supporting
structure 160 for movement, including pivotal, within the
supporting structure 160. For fluorescence imaging, a
purpose-designed, 12.degree. dichroic mirror 104 is placed in the
optical path of light coming from the objective 210 of the
microscope 110. An additional filter 106 selects a narrow 690.+-.10
nm band from the fluorescence signal. The collimated fluorescence
beam is then focused onto a pinhole 108. Two orthogonal
fluorescence polarization states are separated by a polarizing beam
splitter 109 and are registered simultaneously by two identical
balanced photomultiplier tubes 102, 103. An electronic control unit
140 and/or computer 130 allows simultaneous signal processing from
three PMT units 101, 102 and 103. Preferably, a pinhole 124 is
placed before the PMT unit 101. For macro-imaging, a diverging
light beam can be delivered through the objective 210 of the
confocal microscope 110 and used to perform wide-field illumination
for the imaging of the CCD device 240. Alternatively, a separate
illumination device can be utilized--one which does not deliver
illumination through confocal optics 113, 115 of a confocal
microscope 110. The confocal optics of the confocal imager, as
embodied in FIG. 1, can further include various mirrors 114, 116,
117, 118, lenses 123, 107, and filters (e.g., 106), as needed. A
polygon mirror 105 is also provided. A confocal microscope is
described in U.S. Pat. No. 5,381,224 to Dixon et al., which is
hereby incorporated by reference in its entirety.
[0028] Reflectance and fluorescence macroscopic images can be
acquired using the CCD device 240, which can be coupled to an
image-splitter, such as a 4-band image-splitter, and can be
operatively associated with a macro-lens 245 (FIG. 2). The layout
of the CCD device 240 and lens 245, as best seen in FIG. 2, allows
a variable angle of light incidence onto the amplitude beam
splitter coupled to the CCD device 240. CCD positioning in an image
plane 281, at an angle of 2.alpha. with respect to the object plane
285, would typically result in the distortion of a captured image.
Such distortion can be minimized by placing the CCD imaging lens
245 at the bisection of the angle (2.alpha.) formed between the
object plane and image plane, or at about an angle of .alpha..
[0029] In one preferred embodiment, positioning a CCD device 240 at
a 55.degree. angle, and the CCD lens 245 at a 27.5.degree. angle,
each with respect to the object plane 285, significantly improves
the image quality (see object b of FIG. 3) as compared to an image
obtained with a lens positioned in the same plane, as a CCD device
image plane 281 (see object a of FIG. 3).
[0030] A 4-band amplitude image splitter (not shown) can be
employed for simultaneous reflectance and fluorescence polarization
image acquisition, via a single or multiple CCD devices or other
sensors, as desired. The image splitter can include a collimating
lens, to collimate the light coming from an intermediate image, a
four-sided highly reflective pupil separating pyramid prism, to
split the incident beam in four, and four adjustable mirrors to
fold the beams through the optical system (not shown). The purpose
of the splitter is to simultaneously produce four images of the
object being imaged. The image splitter eliminates artifacts in
difference images due to fluctuations of lamp intensity and patient
motion, as well as speeding up the image acquisition process.
Linearly polarizing filters, neutral density filters, and/or
spectral bandpass filters can be introduced into the optical paths
of the four spatially-separated beams to study reflectance,
fluorescence, and polarization images of the tissue, as desired.
Additionally or alternatively, other imaging techniques, such as
Raman, multi-photon and harmonic generation imaging techniques can
be used.
[0031] Moreover, for optimal image acquisition and processing it is
preferred that the intensity scales of the reflectance and
fluorescence channels do not differ substantially. Reflectance and
fluorescence channels can be balanced by the introduction of the
neutral density filters into the optical path of reflectance
channels. However, throughput of two reflectance and/or two
fluorescence channels may vary. To account and compensate for such
potential differences at the image processing stage, a calibrated
reflectance/fluorescence reference can be placed in the camera
field of view. Specifically, a reference sample can be kept in the
camera's field of view to account for fluctuations in light and the
like. Lateral resolution and the field of view can be controlled by
the magnification lenses. Multiple interchangeable lenses can be
utilized to allow different magnifications, depending on the
dimensions of the area or region under investigation. The
macro-imaging field of view is preferably about 20-30 mm (with
lateral resolution not worse than 60 .mu.m).
[0032] Image acquisition and analysis is accomplished as follows.
First, macro-images are acquired. Then, the macro-images are
inspected by a physician or an investigator who creates a list in a
computer memory or otherwise notes suspicious areas that require
closer inspection by, for example, confocal imaging. Such listing
can be achieved by pointing at the desired regions using a computer
input device such as a mouse, touch screen or digitizing pad, for
example. Alternatively, such images can be analyzed and listed by a
computer system, based on predetermined search characteristics,
such as image characteristics corresponding to a particular type of
skin cancer.
[0033] As shown in FIG. 2, the intersection of an observation line
(or optical axis, depending on the frequency regime in which the
system is chosen to operate) 211 of the confocal system 110 with
the confocal imaging plane 217 can be used to define the (0;0;0)
point 215 of a Cartesian system of coordinates, so that the (x;y;z)
coordinates of the areas of interest can be easily determined using
computer code. A translation stage 260, which can be provided, can
be capable of movement in three dimensions. Alternatively, if
desired, the imager device itself can be automatically moved to the
corresponding areas of interest on the object to be imaged. The
object to be imaged can be, for example, a patient's skin.
Subsequently, reflectance, fluorescence, and fluorescence
polarization images for each location of interest are acquired and
displayed side by side with macro-images, and can be analyzed. Such
images can be acquired via a confocal optical system, if the device
and system are so-equipped. An example of combined images, a-f, is
presented in FIG. 3.
[0034] As can be seen in FIG. 2, when the device 100 is configured
to image a region with the wide-field imaging modality, via CCD
device 240, the relative orientation of the observation line (e.g.,
optical axis) 241 of the CCD device 240 and the observation line
211 of the high-resolution imaging device 110 is known. Preferably,
such axes intersect at about the surface of the object to be
imaged. Naturally, the device can be adjusted as needed.
[0035] If the imaging devices 110 and 240 need to be repositioned
with respect to the object surface 270, such movement can be
achieved automatically or manually, by an operator. Both imaging
modalities are preferably supported by a common physical structure
to enable movement over the object surface. Moreover, since the
lens 245 and its plane 283 preferably bisect the angle between the
object plane 285 and the CCD image plane 281, such adjustment would
require adjustment of the angles of the lens 245 and CCD device
240. Accordingly, these elements are preferably pivotally mounted
with respect to the aforementioned structure.
[0036] Further, since the embodiment of FIGS. 1 and 2 includes
illumination provided via confocal optics 113, 115, the objective
210 of the confocal microscope must be capable of adjusting in the
Z-axis direction in order to both provide illumination for the
wide-field imaging modality and for confocal imaging.
[0037] FIG. 3 illustrates an example image set that can be output
by systems in accordance with the present technology. FIG. 3, for
example, illustrates images of infiltrative BCC (basal cell
carcinoma). As indicated, image a of FIG. 3 is a wide-field image
of a region of concern. Images b-d of FIG. 3 are high resolution
reflectance images of respective areas of the wide-field image of
image a of FIG. 3, selected by an operator or computer, to be
acquired. The relative positions of each of these areas can be seen
from the white rectangles superimposed on image a. Similarly,
images e-g of FIG. 3 are high-resolution fluorescence images of
these same regions, respectively. The remaining images h and i are
frozen histopathological samples used as a reference by the
operator.
[0038] As can be seen, an operator can have an array of information
at his or her fingertips on which to base a diagnosis. The operator
can choose which imaging technique(s) to utilize, and can switch
between images or imaging techniques, which greatly enhances
operator efficiency.
[0039] The methods and systems of the present technology, as
described above and shown in the drawings, provide for wide-field
and high-resolution imaging with superior characteristics. It will
be apparent to those skilled in the art that various modifications
and variations can be made in the device and method of the present
technology without departing from the spirit or scope of the
invention. Thus, it is intended that the present invention include
modifications and variations that are within the scope of the
appended claims and their equivalents.
* * * * *