An imaging system for navigating surgery for non-contact, multi-scale in VIVO photoacoustic, ultrasound, and fluorescence imaging

Abstract

An imaging system for multi-scale, non-contact US, PA, and FL imaging with a spatiotemporal sampling scheme, scanning with light integrated with mechanical mirror scanning pathway and testing instantaneous mechanical pressure and FL emission over target tissue surface. The imaging system provides deep and wide tissue imaging using a scanning laser vibrometry with broad tissue excitation using, for example, a tunable pulsed laser and fast microscopic imaging of identified regions of interest using an optic attachment to the camera to secure the tight focusing on the tissue surface. In some configurations, a raster¬ scanning photoacoustic imaging with a fast pulsed laser and parallelized data acquisition is used.

Description

PCT / US25 / 46520 16 September 2025 (16.09.2025)Attorney Docket No. 0184.0324-PCT / P18079-02AN IMAGING SYSTEM FOR NAVIGATING SURGERY FOR NON-CONTACT, MULTI-SCALE IN VIVO PHOTO ACOUSTIC, ULTRASOUND, AND FLUORESCENCE IMAGINGGOVERNMENT FUNDING

[0001] This invention was made with funding provided by U.S. Department of Health and Human Services Advanced Research Projects Agency for Health (ARPA-H) Precision Surgical Interventions (PSI) Program PSI-112: 75N99223R0004. The government may have certain rights in the invention.CROSS REFERENCE TO RELATED APPLICATIONS

[0002] This application claims priority to U.S. Provisional Patent Application No.63 / 695,444 filed on September 17, 2024, the contents of which are hereby incorporated by reference in its entirety.FIELD

[0003] This disclosure relates generally to precision surgical methods, and specifically to an imaging system for structure localization.BACKGROUND

[0004] While technological progress has reshaped surgical practices, the ability to distinguish cancerous from healthy tissues remains a hurdle, alongside the risk of harming vital structures like nerves and blood vessels. What is needed is a platform, including a camera and a clinical workflow, that can be used in both open and laparoscopic surgical procedures, offering enhanced sensitivity and specificity in surgical procedures and in vivo pathology in multi-scales.SUMMARY

[0005] An imaging system in accordance with embodiments of the present disclosure includes a platform that provides a definition of surgical margins and provides a demarcationPCT / US25 / 46520 16 September 2025 (16.09.2025) of nerve network, vasculatures, and tumor extents as critical structures. The platform combines the precision of microscopy for high-resolution surface fluorescence (FL) imaging with wide width and deep depth of non-contact ultrasound (US) and photoacoustic (PA) modalities for tissue examination. The system can be integrated with robotic surgical systems, such as for prostate surgery, or can be adapted to non-robotic settings, for example, to accommodate breast cancer surgeries. Tumor-specific molecular markers are used to achieve sensitivity and specificity in tumor detection. The imaging system accommodates automated image reconstruction, classification, and visualization. The platform can adapt to diverse surgical environments, providing visual guidance for both robotic and traditional procedures.

[0006] The imaging system includes a camera for multi-scale, non-contact US and PA imaging with a spatiotemporal sampling scheme, scanning with excitation light and laser vibrometry (LVM) beams integrated with mechanical mirror scanning pathways (e.g., micro- electro-mechanical systems, galvanometers, etc.) and generating and / or detecting mechanical pressure over the scanning area surface. The camera provides US and PA imaging of deep and wide tissue volume by beamforming acoustic signals obtained from spatially distributed area of the tissue surface. In addition, the camera provides fast microscopic imaging of identified regions of interest using a mechanical focusing adjustment of optical assembly or attaching an additional optics to the end of the camera to secure tight focusing on the tissue surface. A photo detecting sensor or array can be integrated to the main optical pathways for FL imaging in addition to non-contact US and PA imaging. Light source could be standalone pulsed tunable light source for US, PA, and / or FL imaging or be composed with multiple pulsed- and continuous-wave light sources for optimal multi-modal imaging. In some configurations, a raster-scanning US and PA imaging with a fast pulsed laser and parallelized multi-channel LVM is used for faster scanning speed.

[0007] A system of one or more computers can be configured to perform particular operations or actions by virtue of having software, firmware, hardware, or a combination of them installed on the system that in operation causes or cause the system to perform the actions. One or more computer programs can be configured to perform particular operations or actions by virtue of including instructions that, when executed by data processing apparatus, cause the apparatus to perform the actions. One general aspect includes an imaging system for non-contact, multi-scale imaging and spatiotemporal sampling, facilitated by laserPCT / US25 / 46520 16 September 2025 (16.09.2025) vibrometry. The imaging system includes one or more light sources emitting excitation beams, and one or more cameras emitting first detection beams. The one or more cameras are configured to recognize structures and molecular contrast. The imaging system includes a device emitting second detection beams. The device is configured to recognize a depth field over a field of view for beam formation, an optical pathway configured to integrate the excitation beams, the first detection beams, and the second detection beams into a coaxial beam, and scanning mirrors configured with a dynamically reconfigurable optical lens assembly (DYROLA). The DYROLA is configured to enable imaging of features of the structures based on the excitation beams, the first detection beams, and the second detection beams. The DYROLA is configured to change a raster scanning resolution selectively in microscopic / macroscopic levels. Other embodiments of this aspect include corresponding computer systems, apparatus, and computer programs recorded on one or more computer storage devices, each configured to perform the actions of the methods.

[0008] Implementations may include one or more of the following features. The one or more light sources may include at least one of PA light source, US light source, or LVM for PA and US signal recording. The LVM may include multi-channel LVM. The device may include a spatial recognition sensor to understand scanning region of interest. The spatial recognition sensor may include a one-dimensional time-of-flight sensor with raster scanning. The device may include an endoscopic stereo camera having back-end calibration. The device may include a structured light illuminator and camera with back-end calibration. The imaging system may include an attachment to the DYROLA configured for insertion into an incision, the attachment being configured to magnify an image. The DYROLA may include motorized optics, an integrated optics chip, and / or adaptive / deformable optic lenses. The imaging system may include a data input channel to receive kinetic information from robot- assisted surgical system to calibrate the DYROLA setup or scanning pattern. The imaging system may include a coherent fiber bundle channeling the one or more light sources to a collimator array. The one or more cameras may include at least one of a visible / white light (VL) camera or a fluoroscopy (FL) camera. The imaging system may include one or more dichroic mirrors configured to reflect some of the excitation beams, the first detection beams, and the second detection beams. The imaging system may include one or more emission filters configured to filter unwanted light from the excitation beams, the first detection beams, and the second detection beams. The imaging system may include a beam splitter configuredPCT / US25 / 46520 16 September 2025 (16.09.2025) to split images across a white light source camera sensor. The imaging system may include an optical condenser configured to focus light from a white light source. The DYROLA may include autonomously switching from macroscopic to microscopic inspection sequences for identified regions of interest. Implementations of the described techniques may include hardware, a method or process, or computer software on a computer-accessible medium.

[0009] One general aspect includes a method for non-contact, multi-scale imaging and spatiotemporal sampling, facilitated by LVM. The method includes emitting excitation beams by one or more light sources, and emitting first detection beams by one or more cameras. The one or more cameras are configured to recognize structures and molecular contrast. The method includes emitting second detection beams by a device. The device is configured to recognize a depth field over a field of view for beam formation. The method includes integrating, by an optical pathway, the excitation beams, the first detection beams, and the second detection beams into a coaxial beam, and imaging of features of the structures, by scanning mirrors configured with a DYROLA, based on the excitation beams, the first detection beams, and the second detection beams. The DYROLA is configured to change a raster scanning resolution selectively in microscopic / macroscopic levels. Other embodiments of this aspect include corresponding computer systems, apparatus, and computer programs recorded on one or more computer storage devices, each configured to perform the actions of the methods.

[0010] Implementations may include one or more of the following features. The one or more light sources may include at least one of photoacoustic light source, ultrasound light source, or LVM. The LVM may include multi-channel LVM. The method may include channeling, by a coherent fiber bundle, the one or more light sources to a collimator array. The one or more cameras may include at least one of a VL camera or a FL camera. The device may include a time-of-flight sensor. The method may include reflecting, by one or more dichroic mirrors, some of the excitation beams, the first detection beams, and the second detection beams. The method may include filtering, by one or more emission filters, unwanted light from the excitation beams, the first detection beams, and the second detection beams. The method may include splitting, by a beam splitter, images across a white light source camera sensor. The method may include focusing, by an optical condenser, light from a white light source. The method may include autonomously switching, by the DYROLA, from macroscopic to microscopic inspection sequences for identified regions of interest.PCT / US25 / 46520 16 September 2025 (16.09.2025)Implementations of the described techniques may include hardware, a method or process, or computer software on a computer-accessible medium.BRIEF DESCRIPTION OF THE DRAWINGS

[0011] The above and / or other aspects and advantages will become more apparent and more readily appreciated from the following detailed description of examples, taken in conjunction with the accompanying drawings, in which:

[0012] FIG. 1 A is a schematic block diagram of a camera in accordance with embodiments of the present disclosure;

[0013] FIG. IB is a graphical representation of light absorption;

[0014] FIG. 2A is a pictorial illustration of a non-contact, single-port, multi-scale PA imaging system in accordance with embodiments of the present disclosure;

[0015] FIG. 2B is a pictorial illustration of a clinical workflow that indicates aggressive tumor and functioning nerve during surgery in a system in accordance with embodiments of the present disclosure;

[0016] FIG. 3 A is photographic depiction of a multi-channel laser vibrometry (LVM) in accordance with embodiments of the present disclosure;

[0017] FIG. 3B is a photographic depiction of a 2-D collimator array and optical fiber bundle for parallelized LVM sensing;

[0018] FIG. 3C is a schematic diagram of a channel expansion using wavelength division multiplexing (WDM) in accordance with embodiments of the present disclosure;

[0019] FIG. 3D a pictorial illustration of non-contact detection of 1cm deep PA signal using a system in accordance with embodiments of the present disclosure;

[0020] FIG. 3E is a pictorial illustration of the use of structured light in spatial sampling;

[0021] FIG. 4 is a flow diagram of clinical flow of an endoscopy system having an imaging system in accordance with embodiments of the present disclosure; and

[0022] FIG. 5 is a flow diagram of a method according to embodiments of the present disclosure.DETAILED DESCRIPTIONPCT / US25 / 46520 16 September 2025 (16.09.2025)

[0023] For the present disclosure to be more readily understood, certain terms are first defined below. Additional definitions for the following terms and other terms may be set forth throughout the specification. If a definition of a term set forth below is inconsistent with a definition in an application or patent that is incorporated by reference, the definition set forth in this application should be used to understand the meaning of the term.

[0024] As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural references unless the context clearly dictates otherwise. Thus, for example, a reference to “a method” includes one or more methods, and / or steps of the type described herein and / or which will become apparent to those persons skilled in the art upon reading this disclosure and so forth.

[0025] It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting. Further, unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this disclosure pertains. In describing and claiming the methods, systems, and computer readable media, the following terminology, and grammatical variants thereof, will be used in accordance with the definitions set forth below.

[0026] Referring now to FIG. 1 A, a schematic diagram of an imaging system in accordance with embodiments of the present disclosure is shown. The imaging system can enable non-contact PA and US, and FL images in microscopic and macroscopic imaging. The imaging system includes an optical pathway 203 with a DYROLA module that enables a scalable, multi-modal contrast on structures and tumor margins during surgeries. Non-contact biomedical acoustic imaging can see through turbid biological tissue with, for example, but not limited to, a ~5-cm imaging depth. For example, a macroscopic volumetric imaging field of view at 0.5-2 mm spatial resolution over >10 mm imaging depth from the tissue surface can identify structures (nerves, tumor, blood vessels). A microscopic imaging field of view at sub-mm spatial resolution over the tissue surface can identify residual cancer cells after the tumor extraction. Through the use of DYROLA, macroscopic imaging mode (low numerical aperture (NA) setup) provides a first imaging depth with 0.5-2 mm spatial resolution.Microscopic imaging mode (high NA setup) provides high spatial resolution and a second imaging depth. A deep learning agent can use this dynamic adjustability for autonomous detection and confirmation of positive tumor margin with 2-cm diameter regions of interestPCT / US25 / 46520 16 September 2025 (16.09.2025)(ROIs). After the macroscopic identifications have been accomplished, microscopic en face imaging is used for autonomously chosen ROIs over a surgical bed with 2-cm diameter by deep learning (DL) agents at 0.5 mm spatial resolution. A modal switch can maintain the structural alignment between microscopic (high NA setup) and macroscopic (low NA setup) imaging modes. A spatial scanning mechanism in accordance with embodiments of the present disclosure enables a scanning duration that assists a surgeon’s performance. The microscopic / macroscopic imaging can provide, for example, <3 min scanning duration and 10 Hz volume update rate, respectively. An endoscopy system including embodiments in accordance with the present disclosure supports laparoscopic and open surgeries to advance various types of surgeries, for example prostate and breast cancer treatments. The width of the ultimate imaging field of view is variable with the registration and mosaicking of the multiple images obtained with mechanical mirror and robotic scanning during the imaging.

[0027] A modular scanning system, for example, but not limited to, an endoscopy system, includes a main module 201, possibly outside a robotic arm, that provides light sources (205 / 207 / 209 for non-contact PA imaging (for example, but not limited to, 690, 785, 808, 915 nm or fully tunable), US imaging (for example, but not limited to, 1470 nm) and LVM at, for example, but not limited to, 1310 or 1550 nm. The robotic arm can include a laparoscopic imager for robot-assisted surgery. In some configurations, the laparoscopic imager can be mounted on a passive arm for use in general laparoscopic surgery. The optical pathway 203 integrates excitation and detection beams. The fiber bundle 219 is connected to an endoscopy part equipped with visible / white light (VL / WL) 211 and FL 213 imaging cameras for structural recognition and molecular contrast. The integrated scanning VL imaging delineates morphological structure that is superimposable over PA and FL contrast and deployable in motion artifact correction. A time-of-flight (TOF) sensor 217 at, for example, but not limited to, 850 nm recognizes the depth field over the field of view (FOV) for beam formation in PA and US imaging. A set of dichroic mirrors 231 and emission (spectral) filters 233 enable PA, FL, and VL imaging. An imaging system in accordance with embodiments of the present disclosure enables the identification of structures and in vivo pathology before and after a surgical tumor resection, respectively. Any wavelengths (visible, near-infrared, infrared) can be used to identify arbitrary target molecules in deep tissue. For example, the FL sensing wavelength could be in the visible / near-infrared range. The TOF wavelength is arbitrary (e.g., 850nm, 915nm, . . .), and LVM sensing and ncUS / SGHPCT / US25 / 46520 16 September 2025 (16.09.2025) excitation wavelengths could be just off from PA / FL imaging wavelengths. Any wavelengths can be mixed and matched for the function to achieve non-contact US / PA and FL imaging, regardless of focusing configuration.

[0028] Continuing to refer to FIG. 1 A, the composition includes distinct light absorbance, causing multiple wavelengths in a PA light source 205 and US light source 207. Non-contact US imaging can be performed to provide morphology and volumetric vector Doppler imaging to characterize the blood vessels in the target volume. The coaxial beam for non-contact PA, US, FL, and VL imaging is sent to a mechanical scanner such as, for example, but not limited to, a Galvano scanner. A DYROLA with motorized optics can either be before or after the scanning mirrors 215, depending on a desired length of the focusing pathway, and enables imaging features such as, for example, but not limited to, spot size, working distance, and FOV in surgeries such as, for example, but not limited to, prostate and breast surgery. The LVM beam may also be scanned. The DM 231 and mirror under the 2-D collimator array can be configured with scanning mirrors. One of the mirrors may be configured as a dichroic mirror to reflect the LVM beam, and beams at other wavelengths will pass through. In some configurations, the positions of the scanning mirrors may be different from the positions depicted in FIG. 1 A.

[0029] The system includes multiple imaging scales and specifications in a single form factor. The DYROLA changes the raster scanning resolution selectively in microscopic / macroscopic levels. In microscopic imaging mode, at 0.5 mm spatial resolution over a 20 mm><20 mm RO I, at least 1.6 billion points are generated. The FL imaging as the primary modality for in vivo pathology can be optimized so that an objective lens provides an instant small-field FL spot of lOOpm* 100pm oversampled with, for example, but not limited to, a 2,048x2,048 sCMOS camera, which yields a pixel interval to represent a physical distance of approximately 0.05 mm, while reducing the total scanning down to 40,000 events. The scan can complete in 160 seconds (2.7 min) at spatial scanning speed at 250 Hz. PA imaging provides extended spatial perception in the depth domain, providing an opportunity to identify other tumor nodules or structures (nerve and blood vessels) underneath the positive tumor margin.

[0030] Continuing to refer to FIG. 1 A, in some configurations, an endoscope for a laparoscopic surgical environment can include a probe that can be inserted through an abdominal window of up to 25 mm. The endoscope, in accordance with embodiments of thePCT / US25 / 46520 16 September 2025 (16.09.2025) present disclosure, provides spatial-temporal-spectral contrast resolutions and volumetric FOV. A mechanical switch interval in the DYROLA module can enable a clinical workflow between macroscopic surgical guidance and microscopic in vivo pathology. The components described herein can be reconfigured without changing the device, given the goal of identifying a positive tumor margin. In some configurations, the diameter of an endoscope head can be <25 mm for laparoscopic prostate surgery. To provide temporal resolution in macroscopic imaging mode, non-contact PA and US imaging images a volumetric FOV through, for example, sparse spatial sampling events over a tissue surface. For example, at a pulse repetition frequency (PRF) of pulse laser diodes (PLDs) at 50 kHz, 5,000 data acquisition events can be used to reconstruct the volume image at 10 Hz, enabling 70x70 scanning grids.

[0031] Referring now to FIG. IB, a graphical illustration of light absorbance is shown. Absorbance is referred to as extinction because of the mechanism used to measure light absorbance, i.e. the higher the absorbance, the lower the penetration, and the higher the extinction in the spectrophotometry. Nerve-specific dye can include, but is not limited to including, PA or PA / FL. LVM wavelength can be any value. For example, LVM wavelength is shown in FIG. IB to be 1310 nm, and can also be 1550nm or 633nm.

[0032] Referring now to FIG. 2A, an example of the electronics for non-contact ultrasound and photoacoustic imaging for performing scanning and image reconstruction in accordance with embodiments of the present disclosure is shown. A hand-held, fully noncontact US imaging device is also shown, but the device does not need to be hand-held. Scanning part 115 includes a scanner 121 and a computing unit 116. In some configurations, the processor 101, for example, but not limited to, an FPGA or an ASIC, controls ADC / DAC 125, the scanner 121, laser excitation events and data transfer to the computing unit 116. The computing unit 116, which can include any of, for example, but not limited to, CPU, GPU, or FPGA, receives data 103 and measures scanning spot positions, calculates 111 the focusing delay, stores the delayed data 119 in a temporal memory to be synthesized with data acquired by other transmit / receive events, extracting the target data for specific voxel beamforming 117, and sums them to reconstruct the voxel intensity 109. Scheduler 107 coordinates scanning spot recognition, scanning, and image reconstruction. The same general process is used with respect to laparoscopic non-contact ultrasound / photoacoustic imaging.PCT / US25 / 46520 16 September 2025 (16.09.2025)

[0033] Referring now to FIG. 2B, a laparoscopic imaging configuration having an endoscopy camera form factor is shown. An analytical acoustic beam field model delivers a scanning pattern 133 for optimal imaging performance with surface curvature compensation 131. Shown is the evaluation of the impact of surface curvature, indicating importance of surface curvature recognition by the time-of-flight camera 105 (FIG. 2 A).

[0034] Referring now to FIG. 3 A, a multi-channel commercially-available LVM module is connected to a coherent optical fiber and a 2-D collimator array as shown in FIG.3B for simultaneous sampling of a region of interest, coupled with a scanner. In some configurations, if the number of LVM modules is increased, spatiotemporal resolution and signal sensitivity can be enhanced. For example, a 49 LVM array with 7x7 scanning grid can cover a 2 mmx2 mm area at approximately 0.3 mm pitch between sensing points, comparable to that of a contact US array. Such a configuration covers a 100 mmx 100 mm area with 2,500 scanning events.

[0035] Referring now to FIG. 3C, a WDM design can enable multiple channels through a single LVM module as shown in FIG. 3 A, so that either further expansion of the number of channels for better imaging performance at the preserved temporal resolution or reducing the number of LVM modules at the preserved spatial resolution can be achieved, depending on the clinical need.

[0036] Referring now to FIG. 3D, the use of an LVM module 301 to detect a characteristic PA signal originating from a black PDMS layer 1-cm deep in chicken breast303 is shown. In some configurations, a synthetic surface aperture focusing (sSAF) technique can be used to maximize the PA and US imaging by maximizing raw spatial-temporal- contrast resolution, frame averaging, phase aberration correction, and adaptive beamforming.

[0037] Referring now to FIG. 3E, structured light can provide flexibility and simplicity in spatial sampling on top of the tissue to excite and receive acoustic signals. For example, if both LVM and excitation source are structured as a line laser, they can be placed orthogonally on the tissue surface. The intersections between light excitation beams and light detection beams are considered a sensing point. The integration of multiple LVM and excitation sources is simplified by aligning any number of systems with the same interval, which may be controllable by having different fixed optics or adaptive optics. By moving the set of straight lines, spatial sampling can be accomplished. The position of the detection (excitation) lines can be fixed, while excitation (detection) lines are moved for surfacePCT / US25 / 46520 16 September 2025 (16.09.2025) scanning. In this case, the system may accomplish the spatial sampling with one mechanical scanner hardware. An external camera may look into the pattern to locate the sensing points on an arbitrary surface curvature. The detection / excitation beam pattern on the surface can be used to recognize the surface curvature.

[0038] Referring now to FIG. 4, shown is a flow chart of the clinical flow of an endoscopy system having an imaging system in accordance with embodiments of the present disclosure. The flow chart illustrates a clinical workflow for non-contact PA, US, and FL imaging with DYROLA and a software application. The software application, not described herein, can provide, for example, but not limited to, nerve and blood vessel identification, tissue characterization, motion artifact correction, and per-operative image registration before deformation. Macroscopic imaging mode delineates the selected structure before tumor resection that can avoid post-operative complications. A transition between macroscopic and microscopic imaging modes, acquired by DYROLA, can enable iterative validation of negative tumor margin.

[0039] Referring now to FIG. 5, method 500 for non-contact, multi-scale imaging and spatiotemporal sampling, facilitated by LVM, includes, but is not limited to including, emitting 502 excitation beams by one or more light sources, and emitting 504 first detection beams by one or more cameras. The one or more cameras are configured to recognize structures and molecular contrast. Method 500 includes emitting 506 second detection beams by a spatial recognition sensor, for example, but not limited to, a time-of-flight sensor, a structured light with back-end calibration, and / or a stereo camera with back-end calibration. The spatial recognition sensor is configured to recognize a depth field over a field of view for beam formation. Method 500 includes integrating 508, by an optical pathway, the excitation beams, the first detection beams, and the second detection beams into a coaxial beam, and imaging 510 features of the structure, by scanning mirrors configured with a DYROLA having motorized optics, based on the excitation beams, the first detection beams, and the second detection beams, the DYROLA being configured to change a raster scanning resolution selectively in microscopic / macroscopic levels.

[0040] While the invention has been described with reference to the exemplary embodiments thereof, those skilled in the art will be able to make various modifications to the described embodiments without departing from the true spirit and scope. The terms and descriptions used herein are set forth by way of illustration only and are not meant asPCT / US25 / 46520 16 September 2025 (16.09.2025) limitations. In particular, although the method has been described by examples, some steps of the method can be performed in a different order than illustrated or simultaneously. Those skilled in the art will recognize that these and other variations are possible within the spirit and scope as defined in the following claims and their equivalents. All patents, patent applications, other publications or documents, and the like cited herein are incorporated by reference in their entirety for all purposes to the same extent as if each individual item were specifically and individually indicated to be so incorporated by reference.

Claims

PCT / US25 / 46520 16 September 2025 (16.09.2025)CLAIMS1. An imaging system for non-contact, multi-scale imaging and spatiotemporal sampling, facilitated by laser vibrometry, the imaging system comprising: one or more light sources emitting excitation beams; one or more cameras emitting first detection beams, the one or more cameras configured to recognize structures and molecular contrast; a device emitting second detection beams, the device configured to recognize a depth and spatial field over a field of view for beam formation; an optical pathway configured to integrate the excitation beams, the first detection beams, and the second detection beams into a coaxial beam; and scanning mirrors configured with an optical lens assembly that is dynamically reconfigurable, the optical lens assembly being configured to enable imaging of features of the structures based on the excitation beams, the first detection beams, and the second detection beams, the optical lens assembly being configured to change a raster scanning resolution and field of view selectively in microscopic / macroscopic levels.

2. The imaging system of claim 1, wherein the one or more light sources comprises at least one of: photoacoustic light source, ultrasound light source, or laser vibrometry (LVM).

3. The imaging system of claim 2, wherein the LVM comprises: multi-channel LVM.

4. The imaging system of claim 1, wherein the device comprises at least one of: a spatial recognition sensor.

5. The imaging system of claim 4, wherein the spatial recognition sensor comprises: a one-dimensional spatial recognition sensor.

6. The imaging system of claim 5, wherein the spatial recognition sensor comprises: a stereo camera having back-end calibration.PCT / US25 / 46520 16 September 2025 (16.09.2025)7. The imaging system of claim 1, further comprising: an attachment to the optical lens assembly configured for insertion into an incision, the attachment configured to magnify an image.

8. The imaging system of claim 1, wherein the optical lens assembly comprises: motorized optics.

9. The imaging system of claim 1, wherein the optical lens assembly comprises: an integrated optics chip.

10. The imaging system of claim 1, wherein the optical lens assembly comprises: adaptive / deformable optic lenses.

11. The imaging system of claim 1, further comprising: a coherent fiber bundle channeling the one or more light sources to a collimator array.

12. The imaging system of claim 1, wherein the one or more cameras comprise at least one of: a visible / white light (VL) camera or a fluoroscopy (FL) camera.

13. The imaging system of claim 1, further comprising: one or more dichroic mirrors configured to reflect some of the excitation beams, the first detection beams, and the second detection beams.

14. The imaging system of claim 1, further comprising: one or more emission filters configured to filter unwanted light from the excitation beams, the first detection beams, and the second detection beams.

15. The imaging system of claim 1, further comprising: a beam splitter configured to split images across a white light source camera sensor.PCT / US25 / 46520 16 September 2025 (16.09.2025)16. The imaging system of claim 1, further comprising: an optical condenser configured to focus light from a white light source.

17. The imaging system as in claim 1, wherein the optical lens assembly comprises: autonomously switching from macroscopic to microscopic inspection sequences for identified regions of interest.

18. A method for non-contact, multi-scale imaging and spatiotemporal sampling, facilitated by laser vibrometry (LVM), the method comprising: emitting excitation beams by one or more light sources; emitting first detection beams by one or more cameras, the one or more cameras configured to recognize structures and molecular contrast; emitting second detection beams by a device, the device configured to recognize a depth field over a field of view for beam formation; integrating, by an optical pathway, the excitation beams, the first detection beams, and the second detection beams into a coaxial beam; and imaging of features of the structures, by scanning mirrors configured with an optical lens assembly that is dynamically reconfigurable, based on the excitation beams, the first detection beams, and the second detection beams, the optical lens assembly being configured to change a raster scanning resolution selectively in microscopic / macroscopic levels.

19. The method of claim 18, wherein the one or more light sources comprises at least one of:PA light source, US light source, or LVM.

20. The method of claim 19, wherein the LVM comprises: multi-channel LVM.

21. The method of claim 18, further comprising: channeling, by a coherent fiber bundle, the one or more light sources to a collimator array.

22. The method of claim 18, wherein the one or more cameras comprise at least one of:PCT / US25 / 46520 16 September 2025 (16.09.2025) a visible / white light (VL) camera or a fluoroscopy (FL) camera.

23. The method of claim 18, wherein the device comprises: a spatial recognition sensor.

24. The method of claim 18, further comprising: autonomously switching, by the optical lens assembly, from macroscopic to microscopic inspection sequences for identified regions of interest.

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