Optoacoustic probe for imaging

Abstract

A probe for imaging of a tissue site is provided. The probe can have a distal end operable to contact the tissue site and a proximal end. The probe can include a laser system that may be configured to generate light from a light source that is transmitted along a light path to generate return signals and return signals when the light reacts with the tissue site. The light path may include a light guide that may extend through a probe housing from the proximal end to the distal end. The probe can also include an optical window disposed within the housing and that may be configured to receive the light from the light guide prior to the light reaching the tissue site.

Description

OPTOACOUSTIC PROBE FOR IMAGINGCROSS REFERENCE TO RELATED APPLICATION

[0001] This application claims priority to U.S. Provisional Application No. 63 / 556,780 (filed 22-February-2024), The entire disclosure of that application is incorporated herein by reference.TECHNICAL FIELD

[0002] The present invention relates in general to the field of medical imaging, and in particular to a system relating to a probe for imaging.BACKGROUND

[0003] Optoacoustic (OA) imaging systems visualize thin tissue slices at a tissue site. A tissue site may contain a variety of tissue structures that may include, for example, tumors, blood vessels, tissue layers, and components of blood. In optoacoustic imaging systems, light is used to deliver optical energy to a planer slice of the tissue site, which as a result of optical absorption with the tissue structures, produce acoustic waves. An image spatially representing the tissue site can be generated by performing image reconstruction on acoustic signals that return to an ultrasound transducer array. Because biological tissue scatters impinging optical energy in many directions the optical energy can be absorbed by tissue structures outside of a targeted region, which can generate acoustic return signals that interferes with the imaging of tissue structures within the targeted region. Typically, the frequencies of signals obtained by OA imaging systems range between 250 MHz to 2.5MHz.

[0004] Optoacoustic imagining systems can be utilized for targeted regions for a breast, prostrate, etc. In some applications, including for prostrate imaging, optoacoustic images can be supplemented with other imaging systems, including ultrasound imaging. Ultrasound imaging utilizes higher frequency transducers, up to 25MHz, to obtain higher resolutions to help diagnosis and imaging guidance.

[0005] Optoacoustic imaging systems typically include optical fibers that couple to a system laser and bring the light into an optoacoustic probe. The fibers split into two linear outputs that use a diffuser to then spread the light uniformly across two spaced output windows. These fibers are both expensive and difficult to work with. In particular, when a fiber malfunctions, the light being emitted by the probe is uneven, and replacement of the fiber is difficult.

[0006] A need exists to improve how light is carried through an optoacoustic probe from a laser light source.BRIEF SUMMARY

[0007] New and useful systems, apparatuses, and methods for providing optoacoustic imaging are set forth in the appended claims. Illustrative embodiments are also provided to enable a person skilled in the art to make use the claimed subject matter.

[0008] Objectives, advantages, and a preferred mode of making and using the claimed subject matter may be understood best by reference to the accompanying drawings in conjunction with the following detailed description of illustrative embodiments.

[0009] In accordance with embodiments herein, a probe for imaging of a tissue site is provided. The probe can have a distal end operable to contact the tissue site and a proximal end. The probe can include a laser system that may be configured to generate light from a light source that is transmitted along a light path to generate optoacoustic return signals and ultrasound return signals when the light reacts with the tissue site. The light path may include a light guide that may extend through a probe housing from the proximal end to the distal end. The probe can also include an optical window disposed within the housing and that may be configured to receive the light from the light guide prior to the light reaching the tissue site.

[0010] Optionally, the light guide may include an input section configured toreceive the light from at least one optical fiber of the laser system. In one aspect, the input section can have a cross-section that is at least one of rectangular or circular. In another aspect, the light guide may be made from at least one of glass, plastic, silicone, or polyester. In one example, the light guide can include a straight section that can extend from an input section to an angled section, and a movable section that may extend from the angled section and terminating in an optical member configured to disperse the light from the light guide. The light guide may also include a light refraction member that can be configured to receive the light dispersed from the light guide and vary the light before the light reaches the window. Optionally, the light refraction member may be replaceable. In another example, the light refraction member can be configured to be movable in relation to the movable section.

[0011] Optionally, the probe can also include a microcontroller that can have one or more processors, and a memory coupled to the one or more processors, wherein the memory stores program instructions. The program instructions may be executable by the one or more processors to actuate an actuator to move the movable section in relation to the light refraction member. In one aspect, the probe can also include a transducer assembly that may have a first transducer on the distal end, and a second transducer on the distal end. The first transducer can be configured to receive the optoacoustic return signals and have an acoustic lens provided over the first transducer. The second transducer may also be configured to receive the ultrasound return signals. In another aspect, the light guide can include a first straight section that may extend through the housing from an input section. The light guide member can also include a second straight section that may also extend through the housing from the input section.

[0012] In accordance with embodiments herein, a method of imaging a first tissue site and a second tissue site can be provided. The method may include actuating a laser system of a first optoacoustic probe for emitting light along a light path that includes a first light guide that extends through the first optoacoustic probe housing and steering the light to the first tissue site utilizing the first light guide. The method may also include imaging the first tissue site based on the light that is steered with the first light guide,varying the light path to steer the light to the second tissue, and imaging the second tissue site based on the light that is steered to the second tissue.

[0013] Optionally, varying the light path to steer the light to the second tissue can include replacing a first light refraction member that receives the light from the first light guide with a second light refraction member that receives the light from the first light guide. Varying the light path to steer the light to the second tissue may also include steering the light to the second tissue site utilizing the second light refraction member, and imaging the second tissue site based on the light that is steered to the second tissue site via the second light refraction member. In one aspect, varying the light path to steer the light to the second tissue can include replacing the first optoacoustic probe with a second optoacoustic probe having a second light guide that extends through the second photoacoustic probe housing. Varying the light path to steer the light to the second tissue may also include steering the light to the second tissue site utilizing the second light guide, imaging the second tissue site based on the light that is steered to the second tissue site via the second light guide. In one example, the method can also include directing the light from the laser system to the first light guide with optical fibers during imaging of the first tissue site and directing the light from the laser system to the second light guide with the optical fibers during imaging of the second tissue site.

[0014] In accordance with embodiments herein, a light guide for an optoacoustic probe for imaging of a tissue site can be provided that may include an input section configured to receive light from at least one optical fiber of a laser system. The light guide can also include a first straight section extending from the input section and configured to guide the light to a first window, and a second straight section extending from the input section and configured to guide the light to a second window.

[0015] Optionally, the input section can have a cross-section that is at least one of rectangular or circular. In one aspect, the light guide may be made from at least one of glass, plastic, silicone, or polyester. In another aspect, the light guide can also include a first angled section extending from the first straight section, and a first movable sectionextending from the first angled section. The light guide may also include a second angled section extending from the second straight section, and a second movable section extending from the second angled section. Tn yet another example, the light guide can also include a first optical member extending from the first movable section and configured to disperse the light to the first window, and a second optical member extending from the second movable section and configured to disperse the light to the second window.BRIEF DESCRIPTION OF THE DRAWINGS

[0016] The foregoing and other objects, features, and advantages of the invention will be apparent from the following more particular description of preferred embodiments as illustrated in the accompanying drawings, in which reference characters refer to the same parts throughout the various views. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating principles of the invention.

[0017] FIG. 1 shows a schematic block diagram illustrating an embodiment of a combined optoacoustic and ultrasound system that may be used as a platform for the methods and devices disclosed herein.

[0018] FIG. 2 shows a side plan view of an embodiment of a probe that may be used in connection with the methods and other devices disclosed herein.

[0019] FIG. 3 shows a side plan view with hidden lines of an embodiment of a probe that may be used in connection with the methods and other devices disclosed herein.

[0020] FIG. 4 shows a light guide used in connection with the methods and other devices disclosed herein.

[0021] FIG. 5 is a schematic block diagram of a microcontroller utilized in connection with the methods and other devices disclosed herein.

[0022] FIG. 6 is a schematic block flow diagram of a method for imaging a tissue site with a probe in connection with the methods and other devices disclosed herein.

[0023] While the invention is amenable to various modifications and alternative forms, specifics thereof have been shown by way of example in the drawings and will be described in detail. It should be understood, however, that the intention is not to limit the invention to the particular embodiments described. On the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention.DETAILED DESCRIPTION

[0024] The following description and drawings are illustrative and are not to be construed as limiting. Numerous specific details are described to provide a thorough understanding. However, in certain instances, well-known or conventional details are not described in order to avoid obscuring the description. References to one or an embodiment in the present disclosure are not necessarily references to the same embodiment; and such references mean at least one.

[0025] Reference in this specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the disclosure. The appearances of the phrase “in one embodiment” in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. Moreover, various features are described which may be exhibited by some embodiments and not by others. Similarly, various requirements are described which may be requirements for some embodiments, but not other embodiments.

[0026] The systems and methods are described below with reference to, among other things, block diagrams, operational illustrations and algorithms of methods and devices to provide optoacoustic imaging with out-of-plane artifact suppression. It isunderstood that each block of the block diagrams, operational illustrations and algorithms and combinations of blocks in the block diagrams, operational illustrations, and algorithms, can be implemented by means of analog or digital hardware and computer program instructions.

[0027] These computer program instructions can be stored on computer-readable media and provided to a processor of a general-purpose computer, special purpose computer, ASIC, or other programmable data processing apparatus, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, implements the functions / acts specified in the block diagrams, operational block or blocks and or algorithms.

[0028] In some cases, frequency domain-based algorithms require zero or symmetric padding for performance. This padding is not essential to describe the embodiment of the algorithm, so it is sometimes omitted from the description of the processing steps. In some cases, where padded is disclosed in the steps, the algorithm may still be carried out without the padding. In some cases, padding is essential, however, and cannot be removed without corrupting the data.

[0029] In some alternate implementations, the functions / acts noted in the blocks can occur out of the order noted in the operational illustrations. For example, two blocks shown in succession can in fact be executed substantially concurrently or the blocks can sometimes be executed in the reverse order, depending upon the functionality / acts involved.

[0030] Reference will now be made in more detail to various embodiments of the present invention, examples of which are illustrated in the accompanying figures. As will be apparent to one of skill in the art, the data structures and processing steps described herein may be implemented in a variety of other ways without departing from the spirit of the disclosure and scope of the invention herein and should not be construed as being limited to the embodiments set forth herein. Rather, these embodiments areprovided so that this disclosure will be thorough and complete, and will fully convey the concept of the disclosure to those skilled in the art.

[0031] Embodiments herein may be implemented in connection with one or more of the systems and methods described in one or more of the following patents, publications, and / or published applications, all of which are expressly incorporated herein by reference in their entireties:

[0032] U.S. Patent 7,999,161, titled “Laser- Activated Nanothermolysis Of Cells” filed July 23, 2007;

[0033] U.S. Patent 9,289,191, titled “System and method for Acquiring Optoacoustic Data and Producing Parametric Maps Thereof’, and filed June 13, 2012;

[0034] U.S. Patent 9,517,055, titled “System And Method For Acquiring Optoacoustic Data And Producing Parametric Maps Using Subband Acoustic Compensation” filed November 25, 2013;

[0035] U.S. Patent 9,724,072, titled “System And Method For Mixed Modality Acoustic Sampling” filed December 13, 2013;

[0036] U.S. Patent 9,456,805, titled “System And Method For Acquiring Optoacoustic Data And Producing Parametric Maps Using Interframe Persistent Artifact Removal” filed December 19, 2013;

[0037] U.S. Publication 2016 / 0199037, titled “System And Method For Acquiring Optoacoustic Data And Producing Parametric Maps thereof’ filed March 22, 2016;

[0038] U.S. Publication 2017 / 0035388, titled “System And Method For Mixed Modality Acoustic Sampling” filed October 18, 2016;

[0039] U.S. Patent 9,792,686, titled “System And Method For Acquiring Optoacoustic Data And Producing Parametric Maps Using Subband AcousticCompensation” filed November 17, 2016;

[0040] U.S. Publication 2017 / 0296151, titled “System And Method For Mixed Modality Acoustic Sampling” filed June 30, 2017;

[0041] U.S. Publication 2013 / 0109950, titled “Handheld Optoacoustic Probe” filed November 02, 2011;

[0042] U.S. Publication 2016 / 0296121, titled “Handheld Optoacoustic Probe” filed May 02, 2016;

[0043] U.S. Patent 8,686,335, titled “System And Method For Adjusting The Light Output Of An Optoacoustic Imaging System” filed December 31, 2011;

[0044] U.S. Patent 9,528,936, titled “System And Method For Adjusting The Light Output Of An Optoacoustic Imaging System” filed March 31, 2014;

[0045] U.S. Publication 2017 / 0108429, titled “System And Method For Adjusting The Light Output Of An Optoacoustic Imaging System” filed December 27, 2016;

[0046] U.S. Patent 9,330,452, titled “Statistical Mapping In An Optoacoustic Imaging System” filed March 11, 2013;

[0047] U.S. Patent 9,836,838, titled “Statistical Mapping In An Optoacoustic Imaging System” filed May 03, 2016;

[0048] U.S. Publication 2018 / 0061050, titled “Statistical Mapping In AnOptoacoustic Imaging System” filed November 06, 2017;

[0049] U.S. Patent 9,610,043, titled “System And Method For ProducingParametric Maps Of Optoacoustic Data” filed June 13, 2012;

[0050] U.S. Publication 2017 / 0100040, titled “System And Method For Producing Parametric Maps Of Optoacoustic Data” filed December 21, 2016;

[0051] U.S. Publication 2013 / 0338501, titled “System And Method For Storing Data Associated With The Operation Of A Dual Modality Optoacoustic / Ultrasound System” fded June 13, 2012;

[0052] U.S. Publication 2013 / 0338475, titled “Optoacoustic Imaging System With Fiber Optic Cable” filed June 13, 2012;

[0053] U.S. Publication 2014 / 0194723, titled “Multi-Layer Coating For Optoacoustic Probe” filed January 13, 2014;

[0054] U.S. Publication 2017 / 0150890, titled “Optoacoustic Probe With Multi - Layer Coating” filed January 31, 2017;

[0055] U.S. Patent 9,615,750, titled “Methods And Compositions For Carrier Agents And Clearing Agents Used In Optoacoustic Imaging Systems” filed June 14, 2012;

[0056] U.S. Publication 2013 / 0116538, titled “Optoacoustic Imaging Systems And Methods With Enhanced Safety” filed October 19, 2012;

[0057] U.S. Publication 2015 / 0297090, titled “Optoacoustic Imaging Systems And Methods With Enhanced Safety” filed January 23, 2015;

[0058] U.S. Publication 2013 / 0289381, titled “Dual Modality Imaging System For Coregistered Functional And Anatomical Mapping” filed November 02, 2012;

[0059] U.S. Patent 9,757,092, titled “Method For Dual Modality Optoacoustic Imaging” filed November 02, 2012;

[0060] U.S. Publication 2014 / 0039293, titled “Optoacoustic Imaging System Having Handheld Probe Utilizing Optically Reflective Material” filed January 22, 2013;

[0061] U.S. Publication 2017 / 0014101, titled “Dual Modality Imaging System For Coregistered Functional And Anatomical Mapping” filed September 27, 2016;

[0062] U.S. Publication 2013 / 0303875, titled “System And Method For Dynamically Varying The Angle Of Light Transmission In An Optoacoustic Imaging System” fded November 02, 2012;

[0063] U.S. Patent 9,445,785, titled “System And Method For Normalizing Range In An Optoacoustic Imaging System” fded December 21, 2012;

[0064] U.S. Patent 9,282,899, titled “System And Method For Detecting Anomalous Channel In An Optoacoustic Imaging System” fded December 21, 2012;

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[0066] U.S. Publication 2016 / 0317034, titled “System And Method For Providing Selective Channel Sensitivity In An Optoacoustic Imaging System” fded July 11, 2016;

[0067] U.S. Patent 9,445,786, titled “Interframe Energy Normalization In An Optoacoustic Imaging System” fded January 22, 2013;

[0068] U.S. Publication 2017 / 0000354, titled “Interframe Energy Normalization In An Optoacoustic Imaging System” fded September 19, 2016;

[0069] U.S. Publication 2014 / 0206978, titled “Probe With Optoacoustic Isolator” fded January 22, 2013;

[0070] U.S. Patent 9,743,839, titled “Playback Mode In An Optoacoustic Imaging System” fded March 15, 2013;

[0071] U.S. Publication 2017 / 0332916, titled “Playback Mode In An Optoacoustic Imaging System” fded July 27, 2017;

[0072] U.S. Patent 9,398,893, titled “System And Method For Diagnostic Vector Classification Support” fded March 11, 2014;

[0073] U.S. Patent 10,026,170, titled “System And Method For Diagnostic VectorClassification Support” filed July 19, 2016

[0074] U.S. Application number 16 / 022,138, titled “System And Method For Diagnostic Vector Classification Support” filed June 28, 2018;

[0075] U.S. Patent 9,730,587, titled “Diagnostic Simulator” filed March 15, 2013;

[0076] U.S. Publication 2017 / 0332915, titled “Diagnostic Simulator” filed July 27, 2017;

[0077] U.S. Patent 8,823,928, titled “Light Output Calibration In An Optoacoustic System” filed March 15, 2013;

[0078] U.S. Patent 9,163,980, titled “Light Output Calibration In An Optoacoustic System” filed July 11, 2014;

[0079] U.S. Patent 9,814,394, titled “Noise Suppression In An Optoacoustic System” filed March 15, 2013;

[0080] U.S. Publication 2018 / 0078144, titled “Noise Suppression In An Optoacoustic System” filed November 13, 2017;

[0081] U.S. Patent 9,733,119, titled “Optoacoustic Component Utilization Tracking” filed March 15, 2013;

[0082] U.S. Publication 2017 / 0322071, titled “Optoacoustic Component Utilization Tracking” filed July 27, 2017;

[0083] U.S. Publication 2015 / 0101411, titled “Systems And Methods For Component Separation In Medical Imaging” filed October 13, 2014;

[0084] U.S. Publication 2015 / 0305628, titled “Probe Adapted To Control Blood Flow Through Vessels During Imaging And Method Of Use Of Same” filed February27, 2015

[0085] U.S. Publication 2016 / 0187481, titled “Opto- Acoustic Imaging System With Detection Of Relative Orientation Of Light Source And Acoustic Receiver Using Acoustic Waves” filed October 30, 2015.

[0086] The terms “optoacoustic image” and “OA image” refer to an image captured by an imaging system that utilizes transmitted light at one or more frequencies into a tissue site and receives optoacoustic return signals at an optoacoustic transducer that are processed to generate optoacoustic image data that is converted into the OA image. In example embodiments, the optoacoustic return signals are in a range between 250 Hz and 2.5 MHz.

[0087] The term “ultrasound image” refers to an image captured by an imaging system that utilizes transmitted light at one or more frequencies into a tissue site and receives ultrasound return signals at an ultrasound transducer that are processed to generate ultrasound image data that is converted into the ultrasound image. In example embodiments, the ultrasound return signals are in a range between 200 MHz and 25 MHz.

[0088] The term “light” shall refer to any and all electromagnetic radiation, including but not limited to UV radiation, visible light, infrared radiation, etc. Light as used herein is in no way limited to the visible spectrum. Light may include characteristics including polarization, wavelength, frequency, etc. When a characteristic of light is changed, enhanced, diminished, altered, etc. the light may be considered converted, changed, enhanced, diminished, altered, etc.

[0089] The term “tissue site” broadly refers to locations or targets of animal and human tissues and organs such as, for example, breast tissue. A tissue site may contain a variety of different “tissue structures” that may include, for example, tumors, blood vessels, tissue layers, and components of blood. As described below, a sinogram may contain a sample recording of acoustic activity occurring over a period of time inresponse to one or more light events impinging on the tissue site. The acoustic activity captured in the sinogram may include an optoacoustic response, i.e., the acoustic signal that is created as a result of the electromagnetic energy being absorbed by materials within the tissue site such as, for example, various tissue structures that absorb the electromagnetic energy. These optical signals result from the release of thermo-elastic stress confinement within the tissue structures in response to the light events.

[0090] The term “light guide” as used herein shall refer to any and all structures of a light path that can receive a light input at an input end and carries the light to an outlet end while changing a direction of the light to provide a more uniform light output as the light traverses therethrough. For the avoidance in doubt, a fiber and / or fiber optic that carries light from an input end to an output end is not a light guide because the fiber and / or fiber optic does not change the direction of light to provide a more uniform light output or spread the light as the light translates from an input end to an output end. In example embodiments the light guide can split and have two separate sections such that a single input end can be provided, and two separate output ends may also be provided. The light guide can also be referred to as a light pipe.

[0091] The term “numerical aperture” as used herein shall refer to a measurement of light gathered onto a specimen, such as tissue being examined. In one example, the numerical aperture can be measured based on the angle of the light emitted compared to the angle of the light received. To this end, when a component, such as an input of a light guide, a light guide, or the like is described as having a numerical aperture, the input of the light guide, the light guide, or the like is made of a material that can adjust the angle of the light in an X-direction and / or Y-direction to vary an angle of the light emitted by the component.

[0092] The term “optical member” shall refer to any and all structures the vary, change, manipulate, etc. characteristics or properties of light. In one example, an optical member can be located at an output end of a light guide to diffuse light therethrough. In another example, the optical member can be a lens, including a convex lens, concavelens, or the like.

[0093] The term “light refraction member” shall refer to any and all structures that have optical properties that causes the light to change direction therethrough. In one example, the light refraction member can be made of the same material as the light guide. In an example, a light refraction member may operate with an optical member to diffuse light uniformly on an object.

[0094] The term “shape” shall refer to giving a particular form. For example, shaping light refers to changing a dimension of light, including increasing or decreasing a dimension, width, length, height, or the like. In another example the light can be shaped from a circular input to an oval output, rectangular output, or the like. In particular, optical components can be used to change the dimensions, of the light compared to an input provided. For the avoidance of doubt, shape does not refer to a change in intensity, power, color, output, or other characteristic of light. While in example embodiments shaping of the light may result in changes in intensity, power, color, output, or other characteristic of light, such changes are not necessary for the shaping of light to occur.

[0095] Provided is an optoacoustic probe and method to deliver the laser light from a laser system to the output of the optoacoustic probe. Instead of utilizing fibers as a light path to deliver light to a window with diffuser, the light path is a light guide. In one example, the optoacoustic probe can use a light guide made of silicone that can be molded in complex shapes and very cost effectively. The light guide can start with a single, simple geometry such as a circle or square and an input that receives light from the laser system. Then the light guide can split into two separate paths for each output / window and can deliver the light in any complex fashion. With this design, the distal end of the light pipe, or light guide, can include an optic to begin to spread the light. Adj acent to that optic is another silicone optic that further spreads the light. These two optics are required to get the radial spread to illuminate the object, or tissue site, that is being sensed by the curved transducer which has a spread of about 130 degrees.The window at the output of the optoacoustic probe can function to seal the probe.

[0096] Turning to FIG. 1, generally, device 100 for dual imaging that may be employed as multimodality, combined optoacoustic and ultrasound system. In an embodiment, the device 100 includes a probe 102 for dual imaging that is connected via a light path 132 and an electrical path 108 to a system chassis 101. The optoacoustic probe 102 includes a housing 103 for housing the components of the optoacoustic probe 102 therein. Within the system chassis 101 is housed a laser system 129 that utilizes one or more lasers to emit the light of the light path 132, and a computing subsystem 128. In one example, the light path 132 is a light guide that receives the light from the laser system 129 and carries the light to the distal end of the device 100.

[0097] The computing subsystem 128 includes one or more computing components for ultrasound control and analysis and optoacoustic control and analysis; these components may be separate, or integrated. In an embodiment, the computing subsystem 128 is or include a microcontroller. The computing subsystem in one example comprises a relay system 110, a triggering system 135, an optoacoustic processing and overlay system 140 and an ultrasound instrument 150. In one embodiment, the triggering system 135 is configured to actuate and control operation of a laser 130 to emit light.

[0098] In an embodiment, the laser system 129 is capable of producing pulses of light of at least two different wavelengths, and at varying frequencies. In one example the pulses of light can be provided to result in optoacoustic return signals having a lower frequency range, such as between 250 Hertz (Hz) and 2.5 Mega Hertz (MHz), and also result in ultrasound return signals having a higher frequency range such as between 20 MHz and 25 MHz. In this manner, the probe 102 can include dual functionality for providing both optoacoustic images and ultrasound images without the need of changing probes.

[0099] The output of the laser 130 of the laser system 129 is delivered to the probe102 via the light path 132. The laser light is emitted on a tissue site 160, or targeted area of a volume, such as a breast or prostrate, resulting in soundwaves being formed as a result of the laser bouncing of objects. These soundwaves are then utilized to provide both optoacoustic images and ultrasound images of the targeted area of the volume for analysis.[000100] One or more displays 112, 114, which may be touch screen displays, are provided for displaying images and all or portions of the device 100 user interface. The display images may include a first image that is an optoacoustic image, and a second image that is an ultrasound image. One or more other user input devices (not shown) such as a keyboard, mouse, and various other input devices (e g., dials and switches) may be provided for receiving input from an operator.[000101] With reference back to FIG. 1, the probe 102 also can include one or more optical windows 103 through which the light is carried on light path 132 can be transmitted to the surface of a tissue site 160, for example, a three-dimensional volume. Optionally, the probe 102 may be placed in close proximity with organic tissue, phantom, or other tissue site 160 that may have one or more inhomogeneities 161, 162, such as e.g., a tumor, within. An ultrasound gel (not shown) or other material may be used to improve acoustic coupling between the probe 102 and the surface of the tissue site 160 and / or to improve optical energy transfer.[000102] Turning now to FIG. 2, The probe 102 extends from a distal end 208 to a proximal end 210. At the distal end 208 of the probe 102 along a side wall is a transducer assembly 211 that can include is a first transducer 212. The first transducer 212 in one example is covered by an acoustic lens 205. In another example, the first transducer 212 is configured to receive optoacoustic return signals having a lower frequency range, such as between 250 Hz and 2.5 MHz. In addition, in one example, at least one light bar 213 is positioned adjacent to the first transducer on the sidewall of the probe 102. The light bars 213 are provided to generate signals that are obtained by the first transducer 212 for imaging. In one example, a first light bar and second light bar areprovided spaced on either side of the first transducer.[000103] Additionally, the transducer assembly 211 can include a second transducer 214 also located on or at a sidewall of the probe 102. In one example, the second transducer 214 is configured to receive ultrasound return signals having a higher frequency range such as between 20 MHz and 25 MHz. In particular, in an embodiment when the probe 102 is utilized as a prostrate probe, the size of a prostate probe is as small as possible for comfort. The limiting factor for how small a prostrate probe can be is based on the transducers at the distal end of the probe. In one example, the probe 102 has a larger protrusion at the distal end 208 of the probe to make space for both the first transducer 212 and second transducer 214, and then the body of the probe thins out for the length of the probe. This is because the housing only needs to hold the wires, or flex, of co-ax connecting the first transducer 212 and second transducer 214 to the system. Therefore, there is more space in the area directly adj acent to the first transducer 212 and second transducer 214 is extended up through the handle.[000104] FIGS. 3 and 4 illustrate an example embodiment of an optoacoustic probe 300 (FIG. 3) that utilizes a light path 304 that is a light guide 305 (FIG. 4) configured to shape light. Illustrated in FIG. 3 is only the distal end 302 of the probe 300 with the top housing removed. As illustrated, the light path 304 in this example is a light guide 305. The light guide 305 in one example is made of a material such that the light guide is a numerical aperture and configured to shape, or adjust, the light in at least one of an X- direction or a Y-direction. To this end, the material contains the light and can increase or decrease a radius of the light in the X-direction and / or increase or decrease a radius of the light in the Y-direction. Consequently, the light output by the light guide can have a different angle than the light input into the light guide. In one example, the light input into the light guide can be at a right angle, whereas the light output from the light guide can be angled, similar to an inverted cone. The material of the light guide can be glass, plastic, polyester-based, optical grade silicone, or the like. In this manner, the material presents a light weight and less expensive manner of conveying light from the laser system through the housing of the probe 300.[000105] The light path 304, an embodiment when a light guide 305 that receives light from a laser system at an input section 307 (Fig. 4). The input section can be any shape, including circular, rectangular, frustoconical, or the like. In one example, instead of receiving light directly from the laser system, the input section 307 receives light from a shortened cable or fiber. For example, the cable and fibers can plug into the back of the optoacoustic probe. This allows the optoacoustic system to have a single cable / bundle such that probes can be interchanged for different uses. In addition, this allows the fibers to be easily replaced without having to replace the entire optoacoustic probe.[000106] Extending from the input section 307 can be a first straight section 306 that is in spaced relation to a second straight section 308 that also extends from the input section 307. The first straight section 306 and second straight section 308 split from the input section with the first straight section 306 extending along a top of the housing while the second straight section 308 extends along a bottom of the housing. In another embodiment, the first straight section 306 and second straight section 308 are separated from one another, and each received an input from a fiber. By having the light guide 305 receive the output of the fiber, if a malfunction in a fiber occurs, the light that enters the light guide 305 from the working fibers refracts within the light guide 305 such that by the time the light is output from the light guide 305, the output is evenly distributed. In this manner, the probe 300 improves on existing probes that utilize fibers that emit the light, because once a fiber malfunctions, the area that that particular fiber was illuminating no longer receives light. As a result, probe 300 has improved light distribution and functionality compared to probes that utilize only fibers. Such redistribution of the light is considered shaping of the light such that a greater area of light is output.[000107] The first straight section 306 terminates into a first angled section 310 that angles towards the top of the housing to further separate from the lower portion of the light guide 305. Similarly, a second angled section 312 extends from the second straight section 308 towards the bottom of the housing to further separate from the lower portion.[000108] Extending from the first angled section 310 is a first movable section 314 that is coupled to a first optical member 316 that distributes the light being conveyed through the light guide 305. In one example the first optical member 316 is an optical lens, The optical lens may be a convex lens or a concave lens. In one example, a mechanical assembly 318 is coupled to the light guide 305 to cause movement of the first movable section 314 to provide movement of the light as desired. The mechanical assembly 318 can include a lever, gear box, electric motor, or the like that moves the first movable section 314, or other section of the light guide 305 so that the light output by the light guide 305 varies or changes location on the tissue site being imaged.[000109] In addition, extending from the second angled section 312 is a second movable section 320 that is coupled to a second optical member 322 that shapes, or distributes the light being conveyed through the light guide 305. Similar to the first optical member 316, the second optical member 322 can be an optical lens, convex lens, concave lens, etc. In addition, the mechanical assembly 318 may be coupled to the light guide 305 to cause movement of the second movable section 320 to provide movement of the light as desired. The mechanical assembly 318 can include a lever, gear box, electric motor, or the like that moves the second movable section 320, or other section of the light guide 305 so that the light output by the light guide 305 varies or changes location on the tissue site being imaged.[000110] Optionally, coupled within the housing adjacent the first optical member 316 is a first light refraction member 324. The first light refraction member 324 may be a lens, convex lens, concave lens, or the like. The first light refraction member 324 can be configured to vary the light being emitted from the light guide 305 to a first optical window 326 before reaching the tissue site being imaged. To this end, the first light refraction member 324 can be replaceable based on the operation of the probe 300. In one example, the first light refraction member 324 is configured to have properties for imaging a breast, whereas alternatively, the first light refraction member 324 can be replaced with a first light refraction member 324 configured to have properties for imaging a prostrate. In this manner, the functionality of the probe 300 can be quicklychanged for multiple different uses. To this end, the light guide, optical members and light refraction members function to provide three different optical members for adjusting the light output that reaches the breast tissue. As a result, enhanced control over the light output is provided.[000111] In one example, the mechanical assembly 318 can be coupled to the first optical member 316 to move the first optical member 316 relative to the first refraction member 324. In one example the mechanical assembly 318 includes components to move both the first optical member 316 relative to the movable first angled section 310 (or vice versa) and move the first optical member 316 relative to the first refraction member 324 (or vice versa). Alternatively, the mechanical assembly 318 only moves the first optical member 316 relative to the first refraction member. In particular, while the moveable sections 314 and 320 are described as moveable herein, any of the other sections that form the light guide 305 can be coupled to the mechanical assembly 318 to be moved relative to each other.[000112] Similarly, coupled within the housing adjacent the second optical member 322 is a second light refraction member 328. The second light refraction member 328 may be a lens, convex lens, concave lens, or the like. The second light refraction member 328 can be configured to vary the light being emitted from the light guide 305 to a second optical window 330 before reaching the tissue site being imaged. To this end, the second light refraction member 328 can be replaceable based on the operation of the probe 300. In one example, the second light refraction member 328 is configured to have properties for imaging a breast, whereas alternatively, the second light refraction member 328 can be replaced with a second light refraction member 328 configured to have properties for imaging a prostrate. In this manner, the functionality of the probe 300 can be quickly changed for multiple different uses.[000113] In example embodiments the first optical window 326 and second optical window 330 can be made of silicone to isolate acoustic noise as compared to other materials such as glass. In particular, in the example the silicone can include silicapowder loaded to make the material an optical grade. The powder can diffuse any acoustic noise due to the impedance mismatch. In some embodiments larger particles of powder are utilized to diffuse the light.[000114] In one example, disposed between the first optical window 326 and second optical window 330 can be an isolator 332. In one example, the isolator can be a gasket that is molded directly to a transducer lens. During the molding process, after lensing the transducer is no longer removed from the mold. Instead, the transducer never leaves the mold and different side walls are used for the lens and isolator. This prevents the need to tape off the isolator and mitigates alignment concerns.[000115] Figure 5 illustrates a schematic block diagram of a microcontroller 500. In one example, the microcontroller 500 is the computing subsystem 128 of FIG. 1. Alternatively, the microcontroller 500 is a component of the computing subsystem 128 of FIG. 1. The microcontroller 500 includes one or more processors 502, and a memory 504 coupled to the one or more processors 502. The memory 504 store instructions that can be executed by the one or more processors 502. The instructions may include instructions to perform processes and methods as described herein. The microcontroller 500 can also include a transceiver 506 for communicating with components and systems of the probe, along with external systems 508. The external systems 508 include imaging systems that have a display 510 in order to display images, including optoacoustic images, ultrasound images, or the like.[000116] The microcontroller 500 also includes a triggering system 512 that is coupled to a light source for providing the light for the probe. In one example, the microcontroller can vary light characteristics including wavelength, intensity, frequency, etc. of the light emitted by the light source utilizing the triggering system 512. Alternatively, the microcontroller 500 or external device 508 may be utilized to vary the light characteristics.[000117] In one example, stored within the memory 504 is an imaging application514. The imaging application 514 includes instructions and is configured to convert optoacoustic return signals into optoacoustic image data that can be provided on a display as a first image and is configured to convert ultrasound return signals into ultrasound image data that can be provided on the display as a second image. In one example, the imaging application 514 converts return signals received that are in the range of frequency range between 250 Hertz (Hz) and 2.5 Mega Hertz (MHz) to convert the optoacoustic return signals into a first image. In addition, the imaging application 514 converts the ultrasound return signals having a frequency range between 20 MHz and 25 MHz to convert the ultrasound return signals into a second image. In addition, the imaging application 514 is configured to actuate the triggering system, including to vary light characteristics during imaging. In another example, the imaging application is configured to store images, communicate images to remote devices, etc.[000118] The microcontroller 500 can also include one or more actuators 516 that operate a mechanical assembly that can include a lever, gear box, electric motor, or the like. In particular, the actuators 516 are configured to vary a movable member, optical member, lens, or the like to vary the location that light is emitted on a tissue site that is being imaged. In one example, the microcontroller can include a first actuator coupled to or configured to move light emitted by a first optical member or first refraction member while a second actuator is coupled to or configured to move light emitted by a second optical member or second refraction member. In one example such first and second actuators may operate separately from one another such that a user can move the light output of a first optical member while the output of a second optical member stays the same.[000119] By utilizing the one or more actuators 516 when imaging a single site, light can be directed towards a target to get enhanced imaging and collect image. In particular, by directing the light towards the target, out of plane artifacts from lighting up targets outside the viewing plane may be eliminated. In this manner, the light can be moved out of plane to collect an image. Then processing can determine if some detail in the direct light image is real or if it is out of plane by comparing targets / details seen in both imagesand comparing intensities. In addition, focusing the light directly onto the target can minimize the amount of scattering and give a better signal to noise at the site. Further, if the light is still filling the whole window of the probe, the energy density can still be below safety limits. In addition, the light can focus within the tissue to obtain better energy density at the site.[000120] Figure 6 illustrates a schematic flow block diagram of a method 600 of imaging a tissue site with a probe. In one example, the probe of FIGS. 1-4 is the dual imaging probe. In another example, the imaging application 514 of FIG. 5 includes the instructions for executing at least some of the steps of the method 600.[000121] At 602, a first optoacoustic probe is coupled to a laser system. In one example, the first optoacoustic probe is the optoacoustic probe of FIGs. 3-4. In one embodiment, the first optoacoustic probe is coupled to or plugged into the laser system. In particular, in such an embodiment, the laser system includes a plurality of optical fibers that receive light emitted from one or more lasers of the laser system. The optical fibers are not of size and shape, nor configured to be disposed through the length of the optoacoustic probe.[000122] At 604, a determination is made whether the laser system is operating correctly. In one example when the laser system includes fibers that carry light from one or more lasers to a light guide of the optoacoustic probe, one of the fibers may be malfunctioning. If malfunctioning the laser light may still be carried to the light guide and evenly diffused from the optoacoustic probe because of advantages of the light guide as described above. Still, in one embodiment, in response to determining a fiber is malfunctioning, at 606, the first optoacoustic probe is removed from the laser system and the malfunctioning fiber can be replaced.[000123] Once a determination is made that the first optoacoustic probe is not malfunctioning, at 608, a first tissue site is examined. In one example, the first tissue site is a breast, while in a second example, the first tissue site is a prostrate. In anotherexample embodiment, during examination, a movable member of the first optoacoustic probe may be actuated to move the location of the light output by the first optoacoustic probe. Tn this manner, the first optoacoustic probe provides enhanced control during examination.[000124] After examination of the first tissue site, a determination is made at 610 whether a second tissue site that is different than the first tissue site is to be examined. In one example the first tissue site can be breast while the second tissue site is a prostrate. In another example, the first tissue site may be a first breast of first size and shape, while the second tissue site is a second breast of a second size and shape. If another tissue site does not need to be examined, then the process is finished.[000125] If a second tissue site is to be examined, then as 612 the optoacoustic system is varied based on the second tissue site. In one example, the first optoacoustic probe is detached from the laser system and a second optoacoustic probe selected based on the second tissue site is attached from examination. In another example, the first optoacoustic probe itself may be modified. For example, a light refraction member may be added, replaced, or removed from the first optoacoustic probe based on the second tissue site to be examined. The light refraction member receives the light output from a light guide within the first optoacoustic probe. By varying the light refraction member, the light provided to a window of the first optoacoustic probe may be varied based on the second tissue site that is examined.[000126] Once the optoacoustic system is varied at 612, at 614 the second tissue site can be examined. In this manner, the optoacoustic probe provides numerous functional advantages when desiring to use the optoacoustic system for examining more than one tissue site. In addition, by using the light guide, not only is functionality improved, but cost is also reduced, and fixing the optoacoustic probe is facilitated.[000127] Thus provided is a light guide with a distal end where a beam of light exits the light guide and couples into focusing optics before exiting the probe head. This iswere the beam shaping occurs in order to have better coupling into the tissue and to provide better signal to noise or improved resolution of the tissue. To this end, the beam shape generated can be tissue specific.[000128] As used in this description and in the following claims, "a" or "an" means "at least one" or "one or more" unless otherwise indicated. In addition, the singular forms "a", "an", and "the" include plural referents unless the content clearly dictates otherwise. Thus, for example, reference to a composition containing "a compound" includes a mixture of two or more compounds. As used in this specification and the appended claims, the term "or" is generally employed in its sense including "and / or" unless the content clearly dictates otherwise.[000129] Unless otherwise indicated, all numbers expressing quantities of ingredients, measurement of properties and so forth used in the specification and claims are to be understood as being modified in all instances by the term "about," unless the context clearly dictates otherwise. Accordingly, unless indicated to the contrary, the numerical parameters set forth in the foregoing specification and attached claims are approximations that can vary depending upon the desired properties sought to be obtained by those skilled in the art utilizing the teachings of the present invention. At the very least, and not as an attempt to limit the scope of the claims, each numerical parameter should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques. Any numerical value, however, inherently contains certain errors necessarily resulting from the standard deviations found in their respective testing measurements.[000130] Those skilled in the art will recognize that the methods and systems of the present disclosure may be implemented in many manners and as such are not to be limited by the foregoing example embodiments and examples. In other words, functional elements being performed by single or multiple components, in various combinations of hardware and software or firmware, and individual functions, may be distributed among software applications at either the client level or server level or both.In this regard, any number of the features of the different embodiments described herein may be combined into single or multiple embodiments, and alternate embodiments having fewer than, or more than, all of the features described herein are possible. Functionality may also be, in whole or in part, distributed among multiple components, in manners now known or to become known. Thus, myriad software / hardware / firmware combinations are possible in achieving the functions, features, interfaces, and preferences described herein. Moreover, the scope of the present disclosure covers conventionally known manners for carrying out the described features and functions and interfaces, as well as those variations and modifications that may be made to the hardware or software or firmware components described herein as would be understood by those skilled in the art now and hereafter.[000131] Furthermore, the embodiments of methods presented and described as flowcharts in this disclosure are provided by way of example in order to provide a more complete understanding of the technology. The disclosed methods are not limited to the operations and logical flow presented herein. Alternative embodiments are contemplated in which the order of the various operations is altered and in which suboperations described as being part of a larger operation are performed independently.[000132] Various modifications and alterations to the invention will become apparent to those skilled in the art without departing from the scope and spirit of this invention. It should be understood that the invention is not intended to be unduly limited by the specific embodiments and examples set forth herein, and that such embodiments and examples are presented merely to illustrate the invention, with the scope of the invention intended to be limited only by the claims attached hereto. Thus, while the invention has been particularly shown and described with reference to a preferred embodiment thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the spirit and scope of the invention.

Claims

WHAT IS CLAIMED IS:

1. A probe for imaging of a tissue site, the probe having a distal end operable to contact the tissue site and a proximal end, the probe comprising: a laser system configured to generate light from a light source that is transmitted along a light path to generate return signals when the light reacts with the tissue site; the light path comprising a light guide that extends through a probe housing from the proximal end to the distal end that is configured to shape the light received by the light guide to provide an output; and an optical window disposed within the housing and configured to receive the light from the light guide prior to the light reaching the tissue site.

2. The probe of claim 1, wherein the light guide is a numerical aperture and configured to adjust the light in at least one of an X-direction or a Y-direction.

3. The probe of claim 1, wherein the light guide includes an input section configured to receive the light from at least one optical fiber or another light guide of the laser system.

4. The probe of claim 3, wherein the input section has a cross-section that is at least one of rectangular or circular.

5. The probe of claim 1, wherein the light guide is made from at least one of glass, plastic, optical grade silicone, or polyester.

6. The probe of claim 1, wherein the light guide comprises: a straight section extending from an input section to an angled section; and a movable section extending from the angled section and terminating in an optical member configured to disperse the light from the light guide.

7. The probe of claim 6, further comprising a light refraction member configured to receive the light dispersed from the light guide and vary the light before the light reaches the window.

8. The probe of claim 7, wherein the light refraction member is replaceable.

9. The probe of claim 7, wherein the light refraction member is configured to be movable in relation to the movable section.

10. The probe of claim 9, further comprising: a microcontroller including one or more processors, and a memory coupled to the one or more processors, wherein the memory stores program instructions, wherein the program instructions are executable by the one or more processors to: actuate an actuator to move the movable section in relation to the light refraction member.

11. The probe of claim 1, further comprising: a transducer assembly including a first transducer on the distal end, and a second transducer on the distal end; the first transducer configured to receive the return signals and having an acoustic lens provided over the first transducer; and the second transducer configured to receive the return signals.

12. A method of imaging a first tissue site and a second tissue site comprising: actuating a laser system of a first optoacoustic probe for emitting light along a light path that includes a first light guide that extends through the first optoacoustic probe housing;steering the light to the first tissue site utilizing the first light guide; shaping the light in at least one of an X-direction or a Y-direction as the light traverses through the light guide; imaging the first tissue site based on the light that is shaped with the first light guide; varying the light path to steer the light to the second tissue; and imaging the second tissue site based on the light that is steered to the second tissue.

13. The method of claim 12, wherein varying the light path to steer the light to the second tissue comprises: replacing a first light refraction member that receives the light from the first light guide with a second light refraction member that receives the light from the first light guide; steering the light to the second tissue site utilizing the second light refraction member; and imaging the second tissue site based on the light that is steered to the second tissue site via the second light refraction member.

14. The method of claim 12, wherein varying the light path to steer the light to the second tissue comprises replacing the first optoacoustic probe with a second optoacoustic probe having a second light guide that extends through the second photoacoustic probe housing; steering the light to the second tissue site utilizing the second light guide; and imaging the second tissue site based on the light that is steered to the second tissue site via the second light guide.

15. The method of claim 14, further comprising: directing the light from the laser system to the first light guide with optical fibers during imaging of the first tissue site; anddirecting the light from the laser system to the second light guide with the optical fibers during imaging of the second tissue site.

16. A light guide for an optoacoustic probe for imaging of a tissue site comprising: an input section configured to receive light from at least one optical fiber of a laser system; the input configured to be a numerical aperture that shapes the light as the light travels along a light path; a first straight section extending from the input section and configured to guide the light to a first window; and a second straight section extending from the input section and configured to guide the light to a second window.

17. The light guide of claim 16, wherein the input section is configured to adjust a radius of the light in at least one of an X-direction or a Y-direction to shape the light.

18. The light guide of claim 16, wherein the light guide is made from at least one of silicone, glass, plastic, or polyester.

19. The light guide of claim 16, further comprising: a first angled section extending from the first straight section; a first movable section extending from the first angled section; a second angled section extending from the second straight section; and a second movable section extending from the second angled section.

20. The light guide of claim 19, further comprising: a first optical member extending from the first movable section and configured to disperse the light to the first window; anda second optical member extending from the second movable section and configured to disperse the light to the second window.

Images