Optical splitter for laser surgical systems with overheating protection

Abstract

To provide systems, devices, and methods for identifying a target in vivo.SOLUTION: A target identification system for use in electrosurgery includes a probe, an optical splitter, and a spectroscopy system. The probe includes an optical pathway to pass a first optical signal to an anatomical target and at least part of a second optical signal from the anatomical target. The optical splitter includes a first port to direct the first optical signal to the optical pathway and to receive the at least part of the second optical signal from the optical pathway, a second port to receive the first optical signal, and a parabolic reflector to redirect the part of the second optical signal. The spectroscopy system can identify a characteristic of the anatomical target based on the redirected at least part of the second optical signal.SELECTED DRAWING: Figure 1

Description

[Technical field]

[0001] This application relates generally to optical surgical systems, and more particularly to techniques for splitting an optical response signal that shares an optical path with an electrosurgical signal and protecting the optical components of the optical surgical system from overheating. [Background technology]

[0002] Claiming priority This application claims the benefit of priority under 35 U.S.C. §119(e) of U.S. Provisional Patent Application No. 63 / 171,636, filed April 7, 2021, which is incorporated herein by reference in its entirety.

[0003] Laser or plasma systems have been used to deliver surgical laser energy to various target treatment areas such as soft or hard tissue. Examples of laser treatments include ablation, coagulation, vaporization, fragmentation, etc. In lithotripsy applications, lasers have been used to destroy stone structures or ablate larger stones into smaller fragments in the kidney, gallbladder, ureter, among other areas of stone formation.

[0004] Endoscopes are commonly used to provide access to internal locations of subjects to give visual access to physicians. Endoscopes are typically inserted into a patient's body to deliver light to a target (e.g., a target anatomical structure or object) being examined and collect signals (e.g., light) reflected from the object. The reflected signals carry information about the object being examined. Some endoscopes include a working channel through which an operator can perform suction, pass instruments such as brushes, biopsy needles, or forceps, or perform minimally invasive surgery to remove unwanted tissue or foreign objects from the patient's body. Summary of the Invention [Problem to be solved by the invention]

[0005] In certain conventional procedures using electromagnetic energy, there is no way to identify one or more characteristics (e.g., type, material, composition, composition profile, structure, or hardness) of an anatomical target while performing the procedure. For health-related procedures, it can be difficult to identify in vivo whether the target is soft or hard tissue. There are several surgical methods that can be used to extract tissue and then identify the composition or other characteristics of the tissue after it has been removed from the body. However, such characteristics cannot be determined in vivo.

[0006] Continuous identification of tissue characteristics during an endoscopic procedure can provide physicians with additional information to better tailor therapeutic approaches during the procedure. However, conventional tissue characterization techniques, which typically require the removal of tissue samples for analysis, are unable to provide continuous monitoring and identification of tissue characteristics throughout the procedure.

[0007] Some endoscopic surgery systems can deliver laser energy to a target treatment area. The laser energy may be inadvertently dissipated in one or more optical components of the endoscopic surgery system, which may cause overheating and damage to such components. The present inventors have recognized, among other things, an unmet need for monitoring the temperature of optical elements during endoscopic surgery to prevent overheating and damage to the components. [Means for solving the problem]

[0008] The present application provides improved systems, devices and methods for continuous in vivo monitoring and identification of tissue characteristics during treatment. In one embodiment of the present disclosure, a technique is provided for splitting an electrosurgical signal for use in electrosurgery (such as ablation of a target) and an optical response signal sharing a common optical path in a surgical system. The optical splitter includes a first port for receiving an optical response signal reflected from the target in response to incident illumination, and a second port for receiving an electrosurgical signal, such as a laser beam from a laser system. The optical splitter includes a reflector that can redirect the optical response signal to a spectroscopy system for analyzing the target characteristics. The reflector can have a guide member, such as an aperture, aligned to pass and direct the electrical signal to the target.

[0009] In another aspect of the present disclosure, a target identification system includes an optical splitter for splitting an electrosurgical signal (e.g., a laser beam) from an optical response signal reflected from an anatomical target in response to, for example, illumination of the anatomical target. The optical splitter includes a parabolic reflector having a biconvex reflective surface that can redirect the optical response signal to a spectroscopic system for analyzing target characteristics. Compared to reflectors of other shapes (e.g., flat reflectors), the parabolic reflector can more efficiently collect and focus a larger amount of optical response, and achieve signal reflection and focusing without additional optical components, thereby reducing system complexity and potential alignment errors. Thus, the reliability of the entire system can be improved.

[0010] In another aspect of the disclosure, techniques are provided for identifying the composition of a target in vivo (inside a patient), such as during a medical procedure at or near a target, such as an anatomical tissue target or a stone target. As an example, in the case of ablation of obstructive tissue, such as a kidney stone, compositional information about the stone can assist in performing the procedure more efficiently and effectively. A target identification system for use in electrosurgery can include a probe having an optical path for simultaneously passing an electrosurgical signal, such as a laser beam, to the target and an optical signal reflected from the target in response to the incident illumination. The system includes an optical splitter optically coupled to the probe. The optical splitter includes a reflector having an opening aligned to pass the electrosurgical signal and direct it toward the target, and a reflective surface for redirecting the reflected optical signal to a spectroscopy system. The spectroscopy system can generate spectral information from the reflected optical signal and identify the target as having a distinct composition. The spectral information can be used to adjust settings of the electrosurgical energy system.

[0011] In yet another aspect of the present disclosure, techniques are provided for monitoring the temperature of optical components in an electrosurgical system and protecting such optical components from overheating or damage. The temperature monitor can be coupled to one or more temperature sensors positioned at respective locations of the optical components, such as opposing surfaces of a reflector in an optical splitter. The temperature monitor can detect a temperature change from a baseline temperature during electrosurgery, or a differential temperature, such as between opposing surfaces of a reflector, measured by the respective temperature sensors. The temperature monitor can generate an overheating diagnosis and adjust the electrosurgical energy settings based on the overheating diagnosis. Temperature monitoring, overheating diagnosis and overheating protection as described in accordance with various embodiments herein can help prevent damage to components and improve the reliability of the electrosurgical system.

[0012] Example 1 is a target identification system comprising: a probe comprising an optical path configured to (i) pass a first optical signal to an anatomical target and (ii) pass at least a portion of a second optical signal from the anatomical target in response to illumination of the anatomical target; an optical splitter coupled to the probe and comprising a first port configured to (i) direct the first optical signal to the optical path and (ii) receive at least a portion of the second optical signal from the optical path, a second port configured to receive the first optical signal generated by a signal generator, and a parabolic reflector configured to redirect at least a portion of the second optical signal; and a spectroscopic system configured to (i) receive at least a portion of the redirected second optical signal and (ii) identify a characteristic of the anatomical target based at least in part thereon.

[0013] In Example 2, the subject matter of Example 1 optionally includes a parabolic reflector that may include a concave surface having a reflective coating configured to reflect and focus at least a portion of the second optical signal toward a third port of an optical splitter coupled to the spectroscopic system.

[0014] In Example 3, the subject matter of any one or more of Examples 1-2 optionally includes a parabolic reflector that may include a guide member configured to pass the first optical signal therethrough, the guide member including an opening in the parabolic reflector spatially aligned with the first port.

[0015] In Example 4, the subject matter of any one or more of Examples 1-3 optionally includes a second one or more reflectors positioned relative to the parabolic reflector and configured to cooperate to direct at least a portion of the second optical signal toward a third port of an optical splitter coupled to the spectroscopic system.

[0016] In Example 5, the subject matter of any one or more of Examples 1-4 optionally includes a first optical signal that can include a laser beam emitted from a laser system optically coupled to the optical splitter via the second port.

[0017] In Example 6, the subject matter of Example 5 optionally includes a shield to prevent over-projection of the laser beam into the optical path.

[0018] In Example 7, the subject matter of any one or more of Examples 5-6 optionally includes at least one temperature sensor associated with the optical splitter for determining a temperature of the optical splitter in response to emission of the laser beam.

[0019] In Example 8, the subject matter of Example 7 optionally includes a controller circuit configured to generate a control signal for adjusting a setting of the laser system based at least in part on the determined temperature.

[0020] In Example 9, the subject matter of any one or more of Examples 1-8 optionally includes an optical splitter that may further include one or more optical lenses configured to direct the first optical signal toward the first port.

[0021] In Example 10, the subject matter of Example 9 optionally includes one or more optical lenses, which may include at least one of a collimating lens, a focusing lens, or a biconvex lens.

[0022] In Example 11, the subject matter of any one or more of Examples 9-10 optionally includes at least one of the one or more optical lenses that can include a reflective coating configured to redirect at least a portion of the second optical signal to the spectroscopic system.

[0023] In Example 12, the subject matter of any one or more of Examples 1-11 optionally includes a spectroscopic system that can be configured to (i) generate a composition profile of the stone target and (ii) identify a type of the stone target based at least in part on at least a portion of the received second optical signal.

[0024] In Example 13, the subject matter of any one or more of Examples 1-12 optionally includes a characteristic of the anatomical target, which may include at least one of the type, material, composition, composition profile, structure, or hardness of the anatomical target.

[0025] In Example 14, the subject matter of any one or more of Examples 1-13 optionally includes a controller circuit configured to generate a control signal for adjusting a setting of the signal generator based at least in part on the received second optical signal of the anatomical target.

[0026] Example 15 is an electrosurgical system comprising: an electrosurgical energy system configured to generate an electrosurgical signal operable to ablate an anatomical target; a probe having an optical path configured to (i) pass the electrosurgical signal to the anatomical target and (ii) pass an optical signal from the anatomical target in response to irradiation incident on the anatomical target; an optical splitter optically coupled to the probe, the optical splitter configured to direct the electrosurgical signal to the optical path of the probe, receive at least a portion of the optical signal from the optical path of the probe, and redirect at least a portion of the received optical signal; and a temperature monitor coupled to at least one temperature sensor, the temperature monitor configured to monitor a temperature of the optical splitter in response to emission of the electrosurgical signal and generate an overtemperature diagnosis of the optical splitter based at least in part on the monitored temperature.

[0027] In Example 16, the subject matter of Example 15 includes an optical splitter that may optionally further include a reflector having an aperture configured to allow the electrosurgical signal to pass therethrough, and the at least one temperature sensor is substantially proximate to the aperture.

[0028] In Example 17, the subject matter of any one or more of Examples 15-16 optionally includes an electrosurgical energy system that may include a laser system configured to emit laser pulses, and a temperature monitor configured to synchronize temperature measurements with the laser pulses.

[0029] In Example 18, the subject matter of any one or more of Examples 15-17 optionally includes (i) an optical splitter that may further include a reflector; (ii) at least one temperature sensor including a first temperature sensor on a non-reflective surface of the reflector; and (iii) a temperature monitor that may be configured to detect a temperature change of the non-reflective surface indicative of at least a portion of the optical signal incident on the non-reflective surface of the reflector and generate an overheating diagnosis based at least in part on the detected temperature change of the non-reflective surface.

[0030] In Example 19, the subject matter of any one or more of Examples 15-18 optionally includes (i) an optical splitter that may further include a reflector; (ii) at least one temperature sensor including a second temperature sensor on a reflective surface of the reflector; and (iii) a temperature monitor that may be configured to detect a temperature change in the reflective surface indicative of at least a portion of the optical signal reflected from the anatomical target and incident on the reflective surface of the reflector, and generate an overheating diagnosis based at least in part on the detected temperature change in the reflective surface.

[0031] In Example 20, the subject matter of any one or more of Examples 15-19 optionally includes (i) an optical splitter, which may further include a reflector; (ii) at least one temperature sensor, which may include a first temperature sensor configured to sense a temperature of a non-reflective surface of the reflector opposite the reflective surface and a second temperature sensor configured to sense a temperature of the reflective surface; and (iii) a temperature monitor, which may be configured to generate an overheating diagnosis based at least in part on a comparison of the temperature of the non-reflective surface and the temperature of the reflective surface.

[0032] In Example 21, the subject matter of Example 20 includes an overheat diagnostic that can optionally include a first indicator of misalignment between the probe and the optical splitter if the temperature of the reflective surface is greater than the temperature of the non-reflective surface, and a second indicator of misalignment between the optical splitter and the electrosurgical or electromagnetic energy system if the temperature of the non-reflective surface is greater than the temperature of the reflective surface.

[0033] In Example 22, the subject matter of any one or more of Examples 15-21 optionally includes a controller circuit configured to generate a control signal for adjusting a setting of the electrosurgical energy system based at least in part on the monitored temperature.

[0034] Example 23 is a method of operating an electrosurgical system including an optical splitter and a probe coupled to the optical splitter, the method including directing an electrosurgical signal to an anatomical target through the optical splitter and the probe; receiving at least a portion of an optical signal reflected from the anatomical target in response to irradiating the anatomical target; redirecting at least a portion of the received optical signal via the optical splitter; monitoring a temperature of the optical splitter via a temperature sensor in response to emitting the electrosurgical signal; and generating an overtemperature diagnosis of the optical splitter based at least in part on the monitored temperature upon determining that the monitored temperature exceeds a predetermined threshold.

[0035] In Example 24, the subject matter of Example 23 optionally includes an electrosurgical signal that may include a laser pulse, and synchronizing temperature monitoring with the laser pulse.

[0036] In Example 25, the subject matter of any one or more of Examples 23-24 optionally includes monitoring a temperature of the optical splitter, including detecting a temperature change of a reflector at the optical splitter indicative of at least a portion of the optical signal incident on the reflector, and generating an overheating diagnosis based at least in part on the detected temperature change.

[0037] In Example 26, the subject matter of Example 25 optionally includes detecting a temperature change in the reflector, which may include detecting a temperature change in at least one of the reflective or non-reflective surfaces of the optical splitter.

[0038] In Example 27, the subject matter of any one or more of Examples 23-26 includes monitoring a temperature of the optical splitter, which may optionally include detecting a first temperature of a non-reflective surface of a reflector in the optical splitter and detecting a second temperature of a reflective surface of the reflector opposite the non-reflective surface, and generating an overheating diagnosis based at least in part on a comparison of the first temperature and the second temperature.

[0039] In Example 28, the subject matter of Example 27 includes an overheat diagnostic that can optionally include a first indicator of misalignment between the optical splitter and the probe if the second temperature is greater than the first temperature, and a second indicator of misalignment between the optical splitter and an electrosurgical or electromagnetic energy system that generates the electrosurgical signal if the first temperature is greater than the second temperature.

[0040] In Example 29, the subject matter of any one or more of Examples 23-28 optionally includes adjusting settings of an electrosurgical energy system for generating the electrosurgical signal based at least in part on the monitored temperature.

[0041] The present technique is described in terms of health-related procedures, but is not limited to such. The Summary of the Invention is an overview of some of the teachings of the present application and is not intended to be an exclusive or comprehensive treatment of the present subject matter. Further details regarding the present subject matter can be found in the detailed description and the appended claims. Other aspects of the present disclosure will become apparent to those skilled in the art upon reading and understanding the following detailed description and viewing the drawings that form a part thereof. Each of the drawings is not to be construed in a limiting sense. The scope of the present disclosure is defined by the appended claims and their legal equivalents. [Brief description of the drawings]

[0042] [Figure 1] FIG. 1 illustrates a schematic diagram of an exemplary target identification system in a surgical system, such as an ablation system. [Figure 2A] FIG. 1A is a schematic diagram illustrating an exemplary target discrimination system including optical splitters each including a hollow flat reflector. [Figure 2B] FIG. 1A is a schematic diagram illustrating an exemplary target discrimination system including optical splitters each including a hollow flat reflector. [Figure 3A] FIG. 1A is a schematic diagram illustrating an exemplary target discrimination system including optical splitters each including a hollow flat reflector. [Figure 3B] FIG. 1A is a schematic diagram illustrating an exemplary target discrimination system including optical splitters each including a hollow flat reflector. [Figure 4A] FIG. 2 is a schematic diagram illustrating an example optical splitter that includes multiple reflectors that cooperate to redirect an optical response signal to a spectroscopic system. [Figure 4B] FIG. 2 is a schematic diagram illustrating an example optical splitter that includes multiple reflectors that cooperate to redirect an optical response signal to a spectroscopic system. [Diagram 5] FIG. 1 illustrates a schematic diagram of an exemplary method for identifying a therapeutic target in a patient's body. [Figure 6]1A-1C are schematic diagrams illustrating an exemplary method for monitoring the temperature of and protecting optical components of an electrosurgical system from overheating. [Figure 7] 7 illustrates generally a block diagram of an example machine 700 capable of performing any one or more of the techniques (eg, methods) discussed herein. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0043] The present specification describes systems, devices and methods for splitting an optical feedback signal reflected by a target within a patient's body from an electrosurgical signal, such as a laser beam generated by a laser system and directed to the target. In this specification, the terms "electrosurgical" and "electromagnetic" are used interchangeably. The target can include an anatomical tissue target (e.g., soft tissue, hard tissue, or abnormal tissue such as cancerous tissue), or a stone target (e.g., kidney or pancreobiliary or gallbladder stone). The optical feedback signal and the electrosurgical signal are combined with a common optical path. The optical splitter enables reliable transmission of the electrosurgical signal with minimal attenuation while simultaneously directing the optical feedback signal to the spectroscopy system with minimal distortion. The spectroscopy system can continuously or recursively identify one or more characteristics of the target (e.g., type, material, composition, composition profile, structure or hardness) in vivo throughout the procedure. Feedback can be provided to the laser system to adjust the laser output based on the spectral information and / or the identified target characteristics. This allows for instant adjustment of the laser settings within the setting range of the original laser settings selected by the user. According to some embodiments, the electrosurgical system includes an overheat protection system that can monitor the temperature of optical components, such as the optical splitter, and adjust the laser output to protect the optical components from overheating, thereby preventing damage to the optical splitter and optical path. The systems and devices discussed herein can be used endoscopically or laparoscopically.

[0044] Identifying tissue characteristics (e.g., type, material, composition, compositional profile, structure, or hardness) in vivo by endoscopy or laparoscopy has many applications. For example, if the composition of a kidney stone is pre-identified, a treatment method can be based, at least in part, on the composition of the stone. For example, when using a laser to break up or "dust" a stone, if the stone is known in advance to have a hard composition, the laser settings can be adjusted to a setting that works more effectively and / or efficiently on hard kidney stones.

[0045] Also, techniques that require the removal of tissue samples to identify the composition cannot monitor the composition of the tissue continuously throughout all or at least a portion of the entire procedure. The present techniques can enable the measurement and analysis of the characteristics (e.g., type, material, composition, composition profile, structure or hardness) of the anatomical or stone target at the tip of the endoscope or laparoscope. These techniques can provide more information during health-related procedures, such as surgical or diagnostic procedures, and allow better tailoring of the therapeutic method during the procedure. For example, if the procedure involves breaking a kidney stone into small pieces, e.g., "pulverizing" the kidney stone, and the kidney stone has a hard surface but a soft core, continuous or other continuous monitoring of the target composition by the endoscope or laparoscope can allow adjustment of the settings of the device that performs the "pulverization" during the procedure, such as, for example, the laser settings of a laser ablation device. Target identification can allow first to provide settings that work better (e.g., more effectively and / or efficiently) against the hard surface of the stone, and then to provide settings that work better against the soft core of the stone.

[0046] FIG. 1 illustrates a schematic of an exemplary target identification system 100 in a surgical system 110, such as an electrosurgical system that uses laser energy to ablate a target 117 in a patient's body. The target 117 may include an anatomical tissue target (e.g., soft tissue, hard tissue, or abnormal tissue such as cancerous tissue) or a stone target (e.g., kidney or pancreatic bile duct or gallbladder stone). The surgical system 110 may include a visualization device, such as an endoscope 101, the target identification system 100, a primary medical device, such as a surgical laser system 102, and an overheat protection system 150. The endoscope 101 may include an endoscopic probe 103, a light source 104, and a display 105. The endoscopic probe 103 may include a camera 106, one or more optical signal communication paths 107, 108, and at least one working lumen 111. A distal portion of the endoscopic probe 103 may be inserted into the patient's body. The light source 104, one or more optical paths 107, 108, and display 105 can enable an end user, such as a doctor or surgeon or a robotic device, to illuminate and view an internal area of ​​a patient's body at or near the distal end 109 of the endoscopic probe 103. The light source 104 can emit electromagnetic radiation (e.g., visible light, infrared light, ultraviolet light, or fluorescent light) via the first optical path 108 to illuminate an area at or beyond the distal end 109 of the endoscopic probe 103. Alternatively, the light source 104 can include illumination lights, such as one or more LEDs of a vision system, disposed at the distal end of the endoscope and configured to illuminate an area proximate to a target 117. In one example, the second optical path 107 can communicate image signal information from the camera 106 at the distal end 109 of the endoscopic probe 103 to signal processing circuitry in the display 105 for displaying an image of the area at or beyond the distal end 109 of the endoscopic probe 103, such as an image of the target 117. In some examples, the second optical path 107 can include one or more components, such as one or more optical fibers, and the display 105 can include an eyepiece for an end user to observe an area at or beyond the distal end 109 of the endoscopic probe 103.In certain examples, the second optical path 107 can couple view image signal information from the camera 106 to the display 105, for example, for an end user to view an area at or beyond the distal end 109 of the endoscopic probe 103. In some examples, the camera 106 can be located at or near the proximal end of the endoscopic probe 103, such as near the display 105, and one or more optical fibers can form the second optical path 107 for transmitting image information from the distal end 109 of the endoscopic probe 103 to the camera 106. In some examples, the camera 106 can be located at the distal end 109 of the endoscopic probe 103, and the image information can be transmitted to the display 105 via electrical conductors that form at least a portion of the second optical path 107 integral with the endoscopic probe 103.

[0047] The working lumen 111 may further enable an end user to insert and extract a portion of a primary medical instrument (such as one or more surgical tools) for operating on a target internal region of a patient's body being visualized with the endoscopic probe 103. For example, in the case of the surgical laser system 102, the primary medical instrument may include a working probe 113 and a laser generator 112 for enabling ablation of a target tissue or stone target at or near the distal end 109 of the endoscopic probe 103. In such a system, for an endoscopic or laparoscopic procedure, a laser beam 118 may pass laser energy through the working lumen 111 to treat hard and soft tissue. In certain instances, the surgical laser system 102 may generate a laser beam 118 in a broad wavelength range (e.g., 200 nm to 10,000 nm) from ultraviolet (UV) to infrared (UR). Some lasers can produce output within wavelength ranges that can be highly absorbed by soft or hard tissues, for example, 1900-3000 nm for water absorption, or 400-520 nm for oxyhemoglobin and / or deoxyhemoglobin.

[0048] The target identification system 100 can include an optical splitter 114 (also referred to as a beam splitter) and a spectroscopy system 115. In some examples, the working probe 113 can be part of the target identification system 100. The beam splitter 114 can include (i) a first port 121 for a common optical path 130 that can simultaneously transmit the laser beam 118 and an optical response signal 119, e.g., reflected or emitted from the target 117, (ii) a second port 122 for an optical path coupled to the surgical laser system 102, and (iii) a third port 123 for a feedback optical path coupled to the spectroscopy system 115. The spectroscopy system 115 can include a spectrometer 128 and an optional feedback analyzer 116. In one example, the target identification system 100 can use information from the optical response signal 119 to assist in identifying one or more characteristics (e.g., material or composition) of the target 117. The optical response signal 119 may include, for example, light visible to the human eye, fluorescent light, ultraviolet light, infrared light, or combinations thereof.

[0049] In certain examples, the information in the optical response signal 119 can be used to perform a procedure more efficiently. In one example, electromagnetic radiation from the light source 104 incident on a target can be reflected from a target 117 in an internal area of ​​the patient's body at or near the distal end 109 of the endoscopic probe 103 or can cause the target 117 to emit optical information, such as, for example, fluorescence. The optical information conveyed via the optical response signal 119 is also referred to herein as image response information or optical response information. A spectrometer 128 can be optically coupled to the beam splitter 114 and can provide spectral measurements from the optical response signal 119. Examples of the spectrometer 128 can include a Fourier transform infrared (FTIR) spectrometer, a Raman spectrometer, a UV-VIS spectrometer, a UV-VIS-IR spectrometer, or a fluorescence spectrometer, among others.

[0050] Spectroscopy / spectrometry techniques can be used to identify properties (e.g., type, material, composition, composition profile, structure, or hardness) through spectra reflected, transmitted, emitted, absorbed, or not absorbed by a target surface. Optical spectroscopy can provide timely analysis of organic and inorganic materials. In the case of ablation, optical spectroscopy can help provide several advantages, including, for example, but not limited to, integration with fiber laser ablation techniques, non-destructive methods of material chemical composition analysis, real-time or near real-time composition estimation or composition profile, and applicability to the analysis of various types of biological materials: hard and soft tissues, stones, etc. Spectroscopy techniques can be used alone or in combination to analyze the chemical composition of hard or soft tissues and generate digital spectral data. Examples of digital spectral data can include one or more characteristic spectral features extracted from a reference spectrum. Examples of characteristic reflectance features may include reflectance intensity (or normalized reflectance spectrum intensity) at a particular wavelength or across a range of wavelengths, statistics calculated from the reflectance spectrum (e.g., variation in reflectance across two or more different wavelengths, rate of change in reflectance across a range of wavelengths, etc.), or graphical features that represent the morphology of at least a portion of a spectral reflectance curve (e.g., slope, curvature, curve segments, etc.). In some examples, one or more types of spectroscopy, including, but not limited to, color, ultraviolet, far ultraviolet, visible light, near infrared, and fluorescence spectroscopy, may be used with the endoscope 101 to identify the composition of the target 117. In one example, the spectroscopy system 115 may (i) initiate and control the light source 104 to illuminate the target 117, for example, via the first optical path 108 of the endoscopic probe 103, (ii) receive an optical response signal 119 reflected or emitted from the target 117, for example, via an optical path (such as the common optical path 130) of the working probe 113, and (iii) generate spectral data based on the optical response signal 119.

[0051] The feedback analyzer 116 can identify characteristics of the target 117, such as type, material, composition, composition profile, structure or hardness, from the spectral measurements generated by the spectrometer 128 and based on the spectral measurements. In one example, the feedback analyzer 116 can estimate a constituent profile of the material represented by the spectral data and display such estimate. The composition or structure information can be useful to help provide feedback that can be used to perform a surgical procedure more efficiently. For example, the feedback analyzer 116 can compare the spectroscopic response signal to an available database library of tissue composition data. The feedback analyzer 116 can identify the target material composition based on the spectroscopic response signal and suggest a configuration for the surgical laser system 102 to achieve effective tissue treatment for the identified tissue composition. In one example, the feedback analyzer 116 can identify the stone target as one of multiple stone types having distinct compositions, such as tone or stone fragments in stone-forming areas, such as the urinary system, gallbladder, nasal cavity, digestive tract, stomach, or tonsils. In one example, the stone target can be identified as one of stone types having distinct chemical compositions, such as one of calcium phosphate (CaP) stones, magnesium ammonium phosphate (MAP) stones, calcium oxalate monohydrate (COM) stones, cholesterol-based stones, calcium oxalate dihydrate (COD) stones, cystine stones, or uric acid (UA) stones. In another example, the feedback analyzer 116 can identify the anatomical tissue target as one of a plurality of tissue types, such as soft tissue (e.g., muscle, tendon, ligament, blood vessels, fascia, skin, fat, and fibrous tissue), hard tissue such as bone, connective tissue such as cartilage, among others. In some examples, the anatomical tissue target can be identified as one of tissue types having distinct anatomical locations. For example, a kidney tissue target can be identified as one of canal tissue, cortical tissue, medullary tissue, or ureteral tissue. In another example, the identified tissue target can be identified as normal tissue or abnormal tissue (e.g., cancerous tissue).In yet another example, the identified tissue targets can be identified as treatment areas (eg, tumors or polyps to be removed) or non-treatment areas (eg, blood vessels, muscles, etc.).

[0052] In certain examples, the feedback analyzer 116 can provide one or more control signals or control data to adjust settings of the surgical laser system 102. In the example of laser ablation, the feedback analyzer 116 or an intermediate device can include control circuitry to automatically program or adjust laser settings based on target characteristics (e.g., type, material, composition, composition profile, structure, or hardness). Examples of adjusting laser settings can include, among others, delivery or withholding of delivery of a laser beam, or adjustment of laser beam parameters such as wavelength, power, power density, energy, or pulse parameters (e.g., pulse width, pulse rate, amplitude, duty cycle, pulse shape), exposure time, total dosage or energy, or one or more combinations thereof. In some examples, adjustments of laser settings can be limited or constrained to be within individual or multivariate safe operating ranges set based on settings selected by the end user at the start of the procedure, for example.

[0053] In certain examples, the spectroscopy system 115 may optionally communicate with a database 129. In some examples, the database 129 may be a repository for storing measurements and other information associated with a procedure. In some examples, as the database collects more information, the spectroscopy system 115, or a portion thereof, such as the feedback analyzer 116, may interact with the information in the database 129 to determine the most effective use of the laser system 102, for example, based on the spectroscopic information collected or analyzed during the procedure and / or compared to historical information available in the database 129. In certain examples, the database may be capable of providing a time strategy (e.g., laser pulse parameter values ​​and / or temporal variations thereof) for configuring the surgical laser system 102 as the spectroscopic information of the procedure is collected and analyzed. In certain examples, the database 129 may include an internet-based or cloud-based database and may include applications designed to interact with the feedback analyzer 116 or some other portion of the spectroscopy system 115 based on the historical procedure information and / or adapted to the particular spectroscopic information collected during the procedure to assist in the performance of an efficient surgical procedure.

[0054] For example, in the case of a laser ablation system, the laser settings that may be part of a recipe for the configuration of the surgical laser system 102 may include, but are not limited to, laser operation mode (e.g., pulsed or continuous wave), power, energy, frequency, pulse shape, pulse profile, or one or more combinations thereof. In certain examples, the surgical laser system 102 may operate in an automatic mode or a semi-automatic mode, among others. In an automatic mode, the laser settings may be automatically controlled based on the estimated target characteristics (e.g., type, material, composition, composition profile, structure, or hardness). In a semi-automatic mode, the laser settings may be adjusted based on the estimated target characteristics after receiving some confirmation indication of operator approval to make the setting change. The combination of the surgical laser system 102, the spectroscopy system 115, and the feedback analyzer 116 may be used in a continuous in-operation feedback mode to continuously or recursively identify the characteristics (e.g., type, material, composition, composition profile, structure, or hardness) of the target 117 through the working probe 113, for example, and update the laser settings during or throughout the procedure. It will be appreciated that surgical techniques other than laser-based surgical techniques as discussed herein can be used with target identification system 100 without departing from the scope of the present subject matter.

[0055] In certain examples, a single optical path of the working probe 113 of the target identification system 100 can be used to transport a first optical signal (such as the laser beam 118) to and from the target 117 at the distal end 109 of the working probe 113, and can also be used to transport a second optical signal (such as the optical response signal 119) from the distal end 109 of the working probe 113 to the spectroscopy system 115. The beam splitter 114 can merge multiple optical paths into a single optical path or can split optical information from a common optical path (such as the optical path 130) into one or more separate optical paths. The beam splitter 114 can comprise a reflector having a guide member, such as an aperture extending between two opposing faces of the reflector. The guide member or aperture can be aligned to pass the laser beam 118 and direct the laser beam 118 towards the target 117 via the common optical path 130. The guide member can advantageously avoid or substantially reduce attenuation or distortion of the laser energy prior to entering the optical path 130. The reflector has a reflective surface facing the first port 121 and positioned to redirect the incoming optical response signal 119 transmitted through the optical path 130 towards the spectroscopic system 115 through the third port 123. In some examples, the reflective surface includes a wavelength sensitive coating, such as an anti-reflective coating or material, or a dichroic coating or material, or a combination thereof. Materials suitable for anti-reflective coatings include SiO2 (refractive index of about 1.4 to about 1.5), SiO (refractive index of about 1.8 to about 1.9), Si3N4 (refractive index of about 1.9), TiO2 (refractive index of about 2.3), Ta2O5 (refractive index of about 2.1 to about 2.3), MgF2 (refractive index of about 1.4 to about 1.5), BaF2 (refractive index of about 1.47), CaF2 (refractive index of about 1.39), and the like. Examples of beam splitters having hollow reflectors are discussed below with reference to Figures 2A-2B and 3A-3B, etc. Although beam splitter 114 is shown in Figure 1 as part of target identification system 100, its use is not limited thereto.Beam splitter 114 or variations thereof as discussed below with reference to Figures 2A-2B, 3A-3B, and 4A-4B may be used in other optical or electrosurgical systems.

[0056] The overheat protection system 150 can protect optical components of the surgical system 110, such as the beam splitter 114 or a portion thereof, from overheating. Heat accumulation can result from a portion of the laser beam 118 dissipating in the optical components as it passes through the beam splitter 114. Additionally or alternatively, in some examples, a portion of the laser energy incident on the target 117 can be reflected or radiated back to the endoscopic probe 103 and travel through the common optical path 130, scattering on the surface of an optical component, such as the beam splitter 114, causing an internal temperature increase. The overheat protection system 150 can include a temperature monitor 152 electrically coupled to one or more temperature sensors to measure the temperature of the beam splitter 114 or other optical components. In one example, the overheat protection system 150 can include controller circuitry, for example included in the temperature monitor 152, that can generate control signals to the surgical laser system 102 to adjust the settings of the laser generator 112 based on the monitored temperature. For example, in response to the elevated temperature of the beam splitter 114 exceeding a threshold, the controller circuit can temporarily shut down the laser generator 112 or modify one or more laser beam parameters to reduce the laser energy output. In some examples, the temperature monitor 152 can monitor the temperature of each of the different optical components or each of the temperatures at different locations of the optical components. Based on the temperature measurements, the temperature monitor 152 can identify the cause of overheating, for example, due to the laser beam 118 dissipating at the beam splitter 114 or due to reflected laser energy scattering on the beam splitter 114. The temperature monitor 152 can further generate a diagnosis of optical component overheating. Examples of temperature monitors and overheat protection systems are discussed below with reference to, for example, FIGS. 2A-2B and 3A-3B.

[0057] 2A-2B are schematic diagrams illustrating exemplary target identification systems each including a beam splitter including a hollow flat reflector. Target identification system 200A as shown in FIG. 2A is an example of target identification system 100 and includes beam splitter 214A, probe 113, and spectroscopic system 115. Beam splitter 214A can include one or more ports 221, 222, and 223, collimating lens 220, focusing lens 224, and hollow reflector 270. Similar to ports 121, 122, and 123 of beam splitter 114, first port 221 can receive a common optical path 130, such as a surgical fiber in an endoscope, that can simultaneously transmit laser beam 118 toward target 117 and transmit optical response signal 119 reflected or emitted from target 117 back to beam splitter 214A. The second port 222 can receive a second optical path, such as a laser fiber 230, coupled to the surgical laser system 102. The third port 223 can receive a third optical path, such as a spectrometer fiber 240, coupled to the spectroscopy system 115. As shown in FIG. 2A, the laser beam 118 can be directed from the second port 222 to the first port 221 via a collimating lens 220, a focusing lens 224, and a hollow reflector 270. The hollow reflector 270 can be made of metal, glass, or plastic, among other materials. In one example, the hollow reflector 270 is a hollow mirror. The hollow reflector 270 has a reflective surface 271 (also referred to as the "front surface") facing the first port 221 and the common optical path 130, and a non-reflective surface 272 (also referred to as the "back surface") opposite the reflective surface 271, facing the second port 222 and the collimating lens 220 and the focusing lens 224. The hollow reflector 270 can have an aperture 275, such as a through hole, that extends from the front to the back surface of the reflector body. The aperture 275 can be located substantially at the center of the hollow reflector 270. Alternatively, the aperture 275 can be located at other locations of the reflector body away from the center. The aperture 275 can have a particular size and shape and can be aligned with the path of the collimated and focused laser beam 118 to allow the laser beam to pass substantially without obstruction.In some examples, the reflective surface 271 may include a wavelength-sensitive material or coating, such as an AR material, that may be transparent or anti-reflective to the wavelength of the laser, but highly reflective to the wavelength of interest of the optical response signal 119. Thus, much, if not all, of the laser energy may pass from the second port 222 to the first port 221. In some examples, the focusing lens 224 may similarly include a wavelength-sensitive material or coating, that may be transparent or anti-reflective to the wavelength of the laser, but highly reflective to the wavelength of the optical response signal 119, on the surface facing the hollow reflector 270, thereby allowing the laser energy to pass unobstructed while redirecting a portion (if any) of the optical response signal 119 that leaks through the opening 275 of the hollow reflector 270 to the third port 223. The collimating lens 220 , the focusing lens 224 and the aperture 275 may be spatially aligned with the first port 221 such that the laser beam 118 may be directed to the optical path 130 via the first port 221 .

[0058] Among other advantages, the aperture 275 can effectively avoid attenuation or distortion of the laser beam as it passes through the beam splitter 214A before entering the common optical path 130. Furthermore, because the aperture 275 is open to the laser beam 118, the reflector body is less likely to directly interact with the laser beam 118 and absorb the laser energy. Therefore, the chance of heat generation or damage to the reflector body or other optical components of the beam splitter 214A can be reduced, and the safety and reliability of the system can be improved.

[0059] Although only one aperture 275 is shown in the hollow reflector 270, this is for illustration and not limitation. In some examples, the hollow reflector 270 can include two or more apertures spatially spaced from one another to pass respective optical signals. In one example, two separate laser beams can be sent through respective laser fibers via the second port 222 and enter the beam splitter 214A. The first laser beam has an energy level or laser setting for ablating or pulverizing the hard portion of a hard stone or stone target having a first composition, and the second laser beam has a different energy level or different laser setting for ablating or pulverizing the soft portion of a soft stone or stone target having a different second composition. The two laser beams can be collimated and focused by the lenses 220 and 224 and can be directed toward the common optical path 130 through respective apertures on the reflector body.

[0060] In the example shown in FIG. 2A, the hollow reflector 270 is a flat reflector (e.g., a flat mirror) having a flat reflective surface 271 and a flat non-reflective surface 272. The optical response signal 119 reflected or emitted from the target 117 and directed to the beam splitter 214A through the common optical path 130 can be coupled from the first port 221 to the third port 223 via the hollow reflector 270. The flat reflective surface 271 can be positioned to reflect the optical response signal 119 and redirect the reflected optical response signal 219 toward the third port 223 of the beam splitter 214A. In one example, the beam splitter 214A can include a focusing lens 260 to focus the reflected optical response signal 219 toward the third port 223. The focused optical response signal 229 can travel to the spectrometer system 115 via the spectrometer fiber 240.

[0061] When the laser beam passes through an optical device such as a beam splitter, certain optical components may absorb the laser energy and become overheated. As discussed above, the aperture 275 allows a large portion of the laser beam (e.g., 90%, or in some embodiments, 80% or 70%) to pass through the aperture 275 without directly interacting with the reflector 270, which may substantially reduce the chance of heat accumulating in the body of the reflector. However, in certain cases, some laser energy 138 may be dissipated in optical components such as the hollow reflector 270, which may lead to an increase in temperature. This may occur, for example, due to coupling anomalies between the laser system 102 and the beam splitter 214A, misalignment of the laser fiber 230 and the lens system in the beam splitter 214A, or defects in the lens system such as cracks, dust, or deterioration of the collimating lens 220 or the focusing lens 224. Thus, the dissipated laser energy 138 may heat the non-reflective surface (back surface) of the hollow reflector. Additionally or alternatively, in some cases, a portion of the laser beam directed at the target 117 may be reflected or emitted back to the endoscopic probe. The reflected laser beam 148 may return through the common optical path 130 and scatter onto and heat the reflective surface (front surface) of the hollow reflector 270.

[0062] The target identification system 200A may include a temperature monitor 152 for monitoring the temperature of the hollow reflector 270 or a portion thereof. The temperature monitor 152 may be electrically coupled to one or more temperature sensors to detect temperature changes in the hollow reflector 270 in response to the generation of the laser beam 118. The temperature sensor may be a contact sensor or a non-contact sensor. Examples of temperature sensors include thermocouples, thermistors, infrared sensors, bimetallic elements, resistance temperature detectors, fluorescent temperature sensors, temperature sensitive or temperature dependent luminescent materials, among others. In some examples, the temperature monitor 152 may synchronize the sampling of temperature measurements with the laser pulse. For example, the temperature monitor 152 may sample temperature measurements at a sampling rate substantially equal to the laser pulse rate, whereby temperature data is sampled immediately after every laser pulse. Alternatively, the temperature monitor 152 may sample temperature at an integer multiple of the laser pulse rate, whereby temperature measurements are sampled immediately after every N(>2) laser pulses. Since the time of the laser pulse is approximately the time when the dissipating laser energy 138 enters and heats the reflector body, thereby creating a high temperature gradient across the reflector body surface, synchronizing the temperature measurement with the laser pulse can help improve the sensitivity and accuracy of temperature change detection in the hollow reflector 270.

[0063] By way of example and not limitation, as shown in FIG. 2A, the temperature monitor 152 can be electrically coupled to one or more of a first temperature sensor 254 and a second temperature sensor 256, each located on the body of the hollow reflector 270. In one example, the temperature sensor 252 and / or the temperature sensor 254 can be substantially proximate to the aperture 275. As discussed above, the aperture 275 can be positioned in alignment with the collimated and focused laser beam. However, slight misalignment of the laser fiber 230 relative to the beam splitter 214A, or certain imperfections in the collimating lens 220 and / or the focusing lens 224, may cause the laser energy to be more likely to dissipate in the vicinity of the aperture 275 than in other parts of the reflector body away from the aperture 275. Thus, when misalignment occurs, the temperature of the area close to the aperture 275 is more likely to be higher than other areas of the reflector surface. Positioning the temperature sensor in close proximity to the aperture 275 can improve the sensitivity and accuracy of detecting overheating of the reflector due to, for example, misalignment of the laser fiber or imperfections in the lens system.

[0064] The first temperature sensor 254 may be positioned on the non-reflective surface 272 of the hollow reflector 270. The first temperature sensor 254 measures the temperature (T N (1)), and the baseline temperature (T N The temperature monitor 152 can detect the temperature change (ΔT N ), i.e., ΔT N =T N (1)-T N (0) can be detected. Temperature rise ΔT N is the threshold (T N-th ), i.e., ΔT N >T N-thWhen certain conditions are met, such as:

[0065] A second temperature sensor 256 may be positioned on the reflective surface 271. The second temperature sensor 256 measures the temperature (T R (1)), and the baseline temperature (T R The temperature monitor 152 can detect the temperature change (ΔT R ), i.e., ΔT R =T R (1)-T R (0) can be detected. The temperature rise ΔTR is equal to or greater than the threshold (T R-th ), i.e., ΔT R >T R-th etc., the temperature monitor 152 can determine that the temperature increase is significant and that the reflected laser beam 148 scattering onto the reflective surface 271 is causing heating of the hollow reflector 270.

[0066] The temperature monitor 152 can generate an alert or notification of reflector overheating, which can be presented to a user, for example, via the display 105. Additionally or alternatively, the temperature monitor 152 can generate a diagnosis of overheating, which indicates a significant cause of heating. For example, ΔT N >T N-th can generate an overheating diagnosis of coupling faults between the laser system 102 and the beam splitter 214A, misalignment of the laser fiber 230 and the lens system at the beam splitter 214A, or defects in the lens system such as cracks, dust, or deterioration of the collimating lens 220 or the focusing lens 224. R >T R-thIn this case, an overheating diagnosis of misalignment of the common optical path 130 (e.g., surgical fiber) or the probe 113 with the beam splitter 214A can be generated. The diagnostic information can be presented to a user, for example, via the display 105. In some examples, in response to a diagnosis of misalignment, a recommendation for corrective action (e.g., adjusting the alignment or replacing a component, such as an endoscopic probe) can be provided to the user, for example, via the display 105.

[0067] In some examples, the temperature monitor 152 can detect overheating of an optical component, such as the reflector 270, and generate a diagnosis of overheating based on the differential temperature between the reflective surface 271 and the non-reflective surface 272 during the generation of laser energy. For example, the temperature monitor 152 can detect the temperature (T N (1)) and the temperature of the reflecting surface 271 detected by the second temperature sensor 256 (T R (1)) and generate an overheat diagnosis based on the comparison. In one example, the temperature monitor 152 measures a differential temperature T N (1)-T R (1) can be shown. The temperature T of the non-reflective surface N (1) is the temperature of the reflecting surface T R If it is higher than (1) by at least a specified margin, it can produce an indicator of a coupling error between the laser system 102 and the beam splitter 214A, a misalignment between the laser fiber 230 and the lens system in the beam splitter 214A, or a defect in the lens system such as a crack, dust, or deterioration in the collimating lens 220 or the focusing lens 224. R (1) is the temperature T of the non-reflective surface N If it is higher than (1) by a specified margin, an indicator of misalignment between the common optical path 130 (or probe 113) and the beam splitter 214A can be generated.

[0068] In some examples, the temperature monitor 152 can generate and present to the user a recommendation for corrective action based on the overheating diagnosis. R >T R-th , or the differential temperature T R (1)-T N If overheating is detected based on (1) exceeding a certain margin, a recommendation can be presented to the user to realign the probe 113 or the surgical fiber with the beam splitter or to replace the surgical fiber. N >T N-th , or the differential temperature T N (1)-T R If overheating is detected based on (1) exceeding a certain margin, a recommendation to replace or repair the beam splitter can be presented to the user. In some examples, as described above with reference to FIG. 1, in response to detecting overheating of the optical components, the overheating protection system 150 can automatically adjust the settings of the laser system, such as temporarily shutting down the laser generator 112, or modifying one or more laser beam parameters to reduce laser energy emission.

[0069] The beam splitter 214A may include a blast shield 280 proximate the first port 221. The blast shield 280 may prevent the transmitted laser beam from over-projecting and damaging the common optical path 130 (e.g., the surgical fiber in the endoscopic probe 113). The blast shield 280 may also scatter the reflected laser beam 148 traveling through the common optical path 130, preventing the reflected laser beam 148 from refocusing through the lens system and returning to the laser system 102 and interacting with the laser radiation or otherwise damaging the laser system 102.

[0070] 2B shows a schematic example of a target identification system 200B, which is a variation of the target identification system 200A. The target identification system 200B may include a probe 113, a spectroscopic system 115, a temperature monitor 152, and a beam splitter 214B, which is a variation of the beam splitter 214A of the system 200. The beam splitter 214B includes, among other things, a hollow flat reflector 270 and a lens system between the second port 222 and the hollow reflector 270. In contrast to the lens system of the beam splitter 214A, which includes a collimating lens 220 and a focusing lens 224, the lens system of the beam splitter 214B includes a biconvex lens 225 having two convex surfaces with respective radii of curvature. In one example, the two convex surfaces have the same radius of curvature. The bi-convex lens 225 can focus the laser beam 118 exiting the laser fiber 230 and direct it towards the common optical path 130 through an opening 275 in the hollow flat reflector 270. In some examples, the bi-convex lens 225 can include a wavelength-sensitive material or coating on the surface facing the hollow reflector 270 that can be transparent or anti-reflective to the wavelength of the laser, but highly reflective to the wavelength of the optical response signal 119, thereby allowing the laser energy to pass through without blockage, while redirecting a portion (if any) of the optical response signal 119 that leaks through the opening 275 in the hollow reflector 270 to the third port 223.

[0071] Similar to the collimating lens 220 and the focusing lens 224, in some instances, a certain amount of the laser energy 138 may dissipate in the hollow reflector 270 or other optical components, causing overheating of the components, for example, due to coupling anomalies between the laser system 102 and the beam splitter 214B, misalignment of the laser fiber 230 and the lens system in the beam splitter 214B, or defects in the lens system, such as cracks, dust, or deterioration of the biconvex lens 225. The temperature monitor 152 can continuously or recursively monitor the temperature of the reflector via one or more temperature sensors, such as temperature sensors 254 and / or 256, to detect and generate a diagnosis of overheating. An alert or notification of a substantial temperature increase and / or a diagnosis of overheating can be generated and presented to the user. As discussed above with reference to FIG. 2A, in response to detection of heating of the components, the overheating protection system 150 can adjust the settings of the laser system, such as temporarily shutting down the laser generator 112, or modify one or more laser beam parameters to reduce laser energy emission.

[0072] 3A-3B are schematic illustrations of exemplary target identification systems each including a beam splitter including a hollow parabolic reflector. Target identification system 300A as shown in FIG. 3A is a variation of target identification system 200A and can include probe 113, spectroscopic system 115, temperature monitor 152, and beam splitter 314A, which is a variation of beam splitter 214A of system 200A. Beam splitter 314A includes, among other things, collimating lens 220 and focusing lens 224, and hollow reflector 370, made of, for example, metal, glass, or plastic, among other materials. In one example, hollow reflector 370 is a hollow mirror. In contrast to hollow flat reflector 270, hollow reflector 370 is a parabolic reflector with a concave reflective surface 371 and a convex non-reflective surface 372. The optical response signal 119 reflected or emitted from the target 117 and traveling through the common optical path 130 back to the beam splitter 314A can be coupled from the first port 221 through a hollow parabolic reflector 370 to the third port 223. The concave reflective surface 371 can have a particular radius of curvature and be positioned to reflect and focus the incoming optical response signal 119 and redirect the reflected and focused optical response signal 319 towards the third port 223 of the optical splitter 314A. In some examples, the reflective surface 371 can include a wavelength sensitive material or coating, such as an AR material, that can be transparent or anti-reflective to the wavelength of the laser, but highly reflective to the wavelength of interest of the optical response signal 119. Thus, much, if not all, of the laser energy can be passed from the second port 222 to the first port 221. The reflected and focused optical response signal 319 can be transmitted to the spectrometer system 115 via the spectrometer fiber 240. Compared to the beam splitter 214A, which uses a hollow flat reflector 270 to reflect the optical response signal 319 and a separate focusing lens 260 to focus the reflected response signal, the hollow parabolic reflector 370 can achieve signal reflection and focusing without additional optical components, which can help simplify the system complexity, reduce optical alignment errors, and improve the overall system reliability.

[0073] Similar to the hollow flat reflector 270, the hollow parabolic reflector 370 can have an aperture 375, such as a through hole, extending through the reflector body. The aperture 375 can be aligned with the collimated and focused laser beam 118 and can be sized, shaped or otherwise configured to allow the laser beam to pass therethrough without obstruction. In various examples, the aperture 375 can be spatially aligned with the first port 221, such that the laser beam 118 can be directed into the optical path 130 through the first port 221. The aperture 375 can be located substantially in the center of the reflector 370. Alternatively, the aperture 375 can be located in other locations on the reflector body away from the center. Similar to the discussion above with respect to the hollow flat reflector 270, in some examples, two or more apertures can be included in the body of the hollow parabolic reflector 370. Temperature monitor 152 can continuously or recursively monitor the temperature of the reflector via one or more temperature sensors, such as sensors 254 and / or 256, to detect and generate a diagnosis of overheating. Overheat protection system 150 can automatically adjust settings of the laser system based on a detected temperature increase or a diagnosis of overheating of the reflector.

[0074] 3B is a schematic diagram of an example of a target identification system 300B, which is a variation of the target identification system 300A. The target identification system 300B may include a probe 113, a spectroscopic system 115, a temperature monitor 152, and a beam splitter 314B, which is a variation of the beam splitter 314A of the system 300A. The beam splitter 314B includes, among other things, a hollow parabolic reflector 370 and a lens system between the second port 222 and the hollow reflector 270, which includes a biconvex lens 225 similar to that included in the system 200B. The biconvex lens 225 may focus the laser beam 118 exiting the laser fiber 230 and direct it toward the common optical path 130 through an aperture 375 in the hollow parabolic reflector 370.

[0075] As discussed above, in some examples, dissipated laser energy 138 may dissipate within the hollow reflector 370 or other optical components, causing overheating of the components, for example, due to coupling defects between the laser system 102 and the beam splitter 214B, misalignment of the laser fiber 230 and the lens system in the beam splitter 214B, or defects in the lens system, such as cracks, dust, or deterioration of the biconvex lens 225. The temperature monitor 152 can continuously or recursively monitor the temperature of the reflector via one or more temperature sensors, such as sensors 254 and / or 256, detect overheating of the components, such as overheating of the hollow reflector 370, and generate an overheating diagnosis. An alert or notification of the temperature increase and / or overheating diagnosis can be generated and presented to the user. The overheating protection system 150 can automatically adjust the settings of the laser system, such as temporarily shutting down the laser generator 112, or modify one or more laser beam parameters to reduce the laser energy output.

[0076] 4A-B show examples of beam splitters 414A and 414B each including a plurality of reflectors that cooperate to redirect the optical response signal 119 to the third port 223 and ultimately into the spectrometer system 115 via the spectrometer fiber 240. In FIG. 4A, the plurality of reflectors includes a hollow flat reflector 270 similar to that shown in FIGS. 2A-B and one or more additional reflectors, such as a flat mirror 410, positioned relative to the hollow flat reflector 270 and configured to further reflect the optical signal toward the third port 223. Similarly, in FIG. 4B, the plurality of reflectors includes a hollow parabolic reflector 370 similar to that shown in FIGS. 3A-B and one or more additional reflectors, such as a flat mirror 410, positioned relative to the hollow parabolic reflector 370 and configured to reflect the focused optical signal 319 reflected by the hollow parabolic reflector 370 toward the third port 223. The additional reflector or reflectors allow for more convenient positioning of the third port 223 on the beam splitter and coupling to the spectroscopic system 115 .

[0077] 5 is a flow chart illustrating an exemplary method 500 for identifying one or more characteristics of a target and, optionally, operating an electrosurgical system (e.g., a laser system) for treatment in a patient's body based thereon. Electrosurgical energy can be used to ablate targets such as anatomical tissue targets (e.g., soft tissue, hard tissue, or abnormal tissue such as cancerous tissue) or stone targets (e.g., kidney or pancreatic bile duct or gallbladder stones). The method 500 can be implemented in and executed by the surgical system 110. Although the processes of the method 500 are depicted in a flowchart, they are not required to be executed in a particular order. In various examples, some of the processes may be executed in a different order than shown herein.

[0078] At 510, an optical splitter, such as optical splitter 114, or variations thereof, such as any of beam splitters 214A, 214B, 314A, 314B, 414A, or 414B, can be provided for use in electrosurgery. The optical splitter can include a reflector having an aperture, such as a through hole, extending from a reflective surface to a non-reflective surface of the reflector. As shown in Figures 2A-2B, 3A-3B, and 4A-4B and described above with reference to such figures, examples of such reflectors can include a hollow flat reflector 270 having an aperture 275 in the reflector, or a hollow parabolic reflector 370 having an aperture 375 in the reflector.

[0079] At 520, the target and the surrounding environment within the subject's body can be illuminated with electromagnetic radiation, such as generated by the light source 104. The light source can generate electromagnetic radiation in the UV-IR optical range. Examples of electromagnetic radiation include visible light, infrared light, ultraviolet light, or fluorescent light. As discussed above with reference to FIG. 1, the electromagnetic radiation can be directed to the target through an optical path extending along the elongated body of the endoscope. Alternatively, the illumination light may be generated by one or more illumination lights (e.g., LEDs) positioned at the distal end of the endoscope.

[0080] At 530, an optical signal reflected or emitted from the target in response to the electromagnetic radiation can be received by the endoscopic probe. The reflected optical signal can be transmitted through an optical path, such as the common optical path 130 in the endoscopic probe 103. The probe and the optical paths therein can be optically coupled to an optical splitter. As shown in any of Figures 2A-2B, 3A-3B, and 4A-4B, at 540, the reflected optical signal can be reflected by an optical signal reflector and at least a portion of it can be redirected to a port of a beam splitter optically coupled to a spectroscopic system.

[0081] At 550, spectral information indicative of a characteristic of the target (e.g., type, material, composition, composition profile, structure or hardness of the anatomical target) can be generated from the reflected optical signal by a spectroscopic system, such as spectrometer 128. Spectroscopic techniques can be used alone or in combination to analyze the chemical composition of hard or soft tissues and create a composition profile using the digital spectral data. Examples of digital spectral data can include, among others, the reflection intensity at a particular wavelength, statistical characteristics of the reflection across two or more different wavelengths, and graphical characteristics of a graphical representation of the reflection spectrum.

[0082] At 560, characteristics of the target can be identified using the feedback analyzer 116 or the like based on the spectral information. In one example, the target includes a stone target, and the spectral information can be used to identify the stone target as one of a plurality of stone types having distinct compositions, such as stones or stone fragments in a stone-forming area, such as the urinary system, the gallbladder, the nasal cavity, the gastrointestinal tract, the stomach, or the tonsils. In one example, the stone target can be identified as one of a plurality of stone types having distinct chemical compositions, such as one of CaP stones, MAP stones, COM stones, COD stones, cystine stones, cholesterol-based stones, or uric acid (UA) stones. In another example, the target includes an anatomical tissue target, and the spectral information can be used to identify the anatomical tissue target as one of a plurality of tissue types, such as soft tissue (e.g., muscle, tendons, ligaments, blood vessels, fascia, skin, fat, and fibrous tissue), hard tissue, such as bone, connective tissue, such as cartilage, among others. In some examples, the anatomical tissue target can be identified as one of a plurality of tissue types having distinct anatomical locations. For example, a kidney tissue target can be identified as one of canalicular tissue, cortical tissue, medullary tissue, or ureteral tissue. In another example, the identified tissue target can be identified as normal tissue or abnormal tissue (e.g., cancerous tissue). In yet another example, the identified tissue target can be identified as a treatment area (e.g., a tumor or polyp to be removed) or a non-treatment area (e.g., blood vessels, muscle, etc.).

[0083] The spectral information generated at 550 and / or the identification of the target at 560 can be used to control the delivery of electrosurgical energy, such as laser energy, to the target. Method 500 can include an optional step 570 of generating a control signal to adjust a setting of the electrosurgical energy system for emitting an electrosurgical signal based on the identification of the target. In one example, the electrosurgical energy system can be a surgical laser system 102 and the control signal can be generated using the feedback analyzer 116 to adjust a setting of the laser system for emitting a laser beam. As shown in and discussed with reference to any of Figures 2A-2B, 3A-3B, and 4A-4B, an electrosurgical signal, such as a laser beam, can be directed to the target through an aperture in a reflector and an optical path of a probe. Examples of adjusting the laser settings include, among others, delivery or withholding delivery of a laser beam, or can adjust laser beam parameters, such as wavelength, power, power density, energy, or pulse parameters (e.g., pulse width, pulse rate, amplitude, duty cycle, pulse shape), exposure time, total dose or energy, or one or more combinations thereof. In one example, for a stone target or portion thereof comprised of a hard material, the laser system can generate a laser beam having a higher energy to ablate or pulverize the target, and for a stone target or portion thereof comprised of a soft material, the laser system can generate a laser beam having a lower energy to ablate or pulverize the target.

[0084] 6 is a flow chart illustrating a method 600 for monitoring the temperature of optical components, such as those in an optical splitter of an electrosurgical system, and protecting the optical elements from overheating during electrosurgery (e.g., laser ablation of an anatomical tissue or stone target). In one example, method 600 may be implemented in and performed by overheat protection system 150 of surgical system 110.

[0085] At 610, an optical splitter can be prepared for use in electrosurgery. As shown in Figures 2A-2B, 3A-3B, and 4A-4B, examples of such an optical splitter include optical splitter 114, or variations thereof, such as any of beam splitters 214A, 214B, 314A, 314B, 414A, or 414B. The optical splitter can include a reflector having an aperture extending from a reflective surface to a non-reflective surface of the reflector. As shown in Figures 2A-2B, 3A-3B, and 4A-4B, examples of such a reflector can include a hollow flat reflector 270 having an aperture 275 in the reflector, or a hollow parabolic reflector 370 having an aperture 375 in the reflector.

[0086] As shown in any of Figures 2A-2B, 3A-3B, and 4A-4B, at 620, laser energy can be generated by a laser system, such as surgical laser system 102, and directed toward a target through an opening in a reflector and an optical path of an endoscopic probe optically coupled to a beam splitter. The laser energy can be used to ablate a target, such as an anatomical tissue target (e.g., soft tissue, hard tissue, or abnormal tissue such as cancerous tissue), or a stone target (e.g., kidney or pancreatic bile duct or gallbladder stone).

[0087] As described above with reference to Figures 2A-2B, 3A-3B and 4A-4B, the apertures of the reflector (e.g. apertures 275 or 375) allow most of the laser energy to pass through the apertures without interacting with the reflector body, however, in certain cases, some laser energy may be dissipated within the reflector body. This may occur, for example, due to coupling anomalies between the laser system and the beam splitter, misalignment of the laser fiber in the beam splitter with the lens system (e.g. collimating lens 220 and focusing lens 224, or biconvex lens 225), or defects in the lens system such as cracks, dust or deterioration of the lens system. Such laser energy dissipation may cause a temperature rise in the non-reflective surface of the reflector body or a portion thereof. Additionally or alternatively, in some instances, a portion of the laser energy incident on the target during electrosurgery (e.g. ablation of a tissue or stone target) may be reflected or emitted back to the endoscopic probe and scattered on the reflective surface of the reflector, causing heat accumulation there. Overheating of optical components such as reflectors can cause damage to those optical components if not corrected or mitigated in a timely manner. Continuous or recursive temperature monitoring can help identify significant causes of overheating and prevent or reduce damage caused by overheating.

[0088] At 630, the temperature of an optical component, such as a reflector of an optical splitter, can be monitored using, for example, temperature monitor 152. As discussed above, temperature monitor 152 can be coupled to one or more of a first temperature sensor 254 to sense the temperature of a non-reflective surface of the reflector, or coupled to a second temperature sensor 256 to sense the temperature of a reflective surface of the reflector. In one example, the temperature measurement can be synchronized with the laser pulse to help improve the reliability and sensitivity of detecting temperature changes in the reflector.

[0089] At 640, overheating of the reflector can be detected, for example, using the temperature monitor 152. In one example, reflector overheating can be detected based on a temperature change during generation of laser energy relative to a baseline temperature before generation of laser energy. For example, a temperature increase at the non-reflective surface, if it exceeds a certain threshold, can indicate laser energy dissipation at the non-reflective surface of the reflector. A first diagnosis of a coupling anomaly between the laser system and the beam splitter, misalignment between the laser fiber in the beam splitter and the lens system, or a defect in the lens system can be generated and presented to the user, for example, via the display 105. Additionally or alternatively, a temperature increase at the reflective surface, if it exceeds a certain threshold, can indicate reflected laser energy scattering to the reflective surface of the reflector. A second diagnosis of misalignment of the optical paths in the endoscopic probe and the beam splitter can be generated and presented to the user, for example, via the display 105.

[0090] In addition to or instead of using only one temperature sensor, in some examples, the differential temperature between opposing surfaces of the reflector during the generation of laser energy can be used to detect reflector overheating. For example, if the non-reflective surface temperature (measured by the first temperature sensor) is higher than the reflective surface temperature (measured by the second temperature sensor) by a first margin, a first diagnosis of a coupling anomaly between the laser system and the beam splitter, misalignment between the laser fiber in the beam splitter and the lens system, or a defect in the lens system can be generated and presented to the user. If the reflective surface temperature is higher than the non-reflective surface temperature by a second margin, a second diagnosis of misalignment of the optical paths in the endoscopic probe and the beam splitter can be generated and presented to the user.

[0091] The method 600 may include an optional step 650 of adjusting the settings of the laser system in response to detecting an overheated optical component. As discussed above with reference to FIG. 1, the adjustments may be automatically controlled by a feedback controller in the overheat protection system 150. Such adjustments may include, for example, temporarily shutting down the laser generator or modifying one or more laser beam parameters (e.g., pulsed or continuous wave, power, energy, frequency, pulse shape, pulse profile, or one or more combinations thereof) to reduce the laser energy output. In some examples, in response to a diagnosis of misalignment, a recommendation for corrective action (e.g., adjusting the alignment or replacing a component such as an endoscopic probe) may be provided to the user, for example via the display 105.

[0092] 7 illustrates generally a block diagram of an example machine 700 capable of performing any one or more of the techniques (e.g., methods) discussed herein. Portions of this description may be applied to the computing framework of various portions of the surgical system 110, such as the spectroscopy system 115 and the overheat protection system 150.

[0093] In alternative embodiments, the machine 700 may operate as a standalone device or may be connected (e.g., networked) to other machines. In a networked deployment, the machine 700 may operate as a server machine or a client machine, or both in a server-client network environment. In one example, the machine 700 may operate as a peer machine in a peer-to-peer (P2P) (or other distributed) network environment. The machine 700 may be a personal computer (PC), a tablet PC, a set-top box (STB), a personal digital assistant (PDA), a mobile phone, a web appliance, a network router, switch or bridge, or any machine capable of executing (sequentially or otherwise) instructions that specify operations to be performed by the machine itself. Furthermore, although only a single machine is shown, the term "machine" shall also be considered to include any collection of machines that individually or collectively execute a set (or sets) of instructions to perform any one or more of the methods discussed herein, such as cloud computing, software as a service (SaaS), other computer cluster configurations, etc.

[0094] The examples described herein may include or operate by logic or some components or mechanisms. A circuit set is a collection of circuits implemented in a tangible entity that includes hardware (e.g., simple circuits, gates, logic, etc.). The members of a circuit set are flexible over time, essentially allowing the hardware to be changed. A circuit set includes members, whether alone or in combination, that can perform a specified operation when operated. In one example, the hardware of a circuit set can be designed to perform a specific operation (e.g., hardwired). In one example, the hardware of a circuit set can include variably connected physical components (e.g., execution units, transistors, simple circuits, etc.) that include computer-readable media that are physically modified (e.g., magnetically modified, electrically modified, movable arrangement of immutable cohesive particles, etc.) to encode instructions for a specific operation. When connecting the physical components, the basic electrical properties of the hardware components are changed, for example, from an insulator to a conductor or vice versa. The instructions enable the embedded hardware (e.g., an execution unit or a loading mechanism) to create the members of the circuit set in the hardware through the variable connections to perform some of the specific operations during operation. Thus, the computer-readable medium is communicatively coupled to other components of the circuit set members when the device operates. In one example, any of the physical components may be used in two or more members of two or more circuit sets. For example, during operation, the execution unit may be used in a first circuit of a first circuit set at one time and reused by a second circuit in the first circuit set or reused by a third circuit in the second circuit set at a different time.

[0095] The machine (e.g., computer system) 700 may include a hardware processor 702 (e.g., a central processing unit (CPU), a graphics processing unit (GPU), a hardware processor core, or any combination thereof), a main memory 704, and a static memory 706, some or all of which may communicate with each other via an interlink (e.g., a bus) 708. The machine 700 may further include a display unit 710 (e.g., a raster display, a vector display, a holographic display, etc.), an alphanumeric input device 712 (e.g., a keyboard), and a user interface (UI) navigation device 714 (e.g., a mouse). In one example, the display unit 710, the input device 712, and the UI navigation device 714 may be touch screen displays. The machine 700 may further comprise a storage device (e.g., a drive unit) 716, a signal generating device 718 (e.g., a speaker), a network interface device 720, and one or more sensors 721, such as a Global Positioning System (GPS) sensor, a compass, an accelerometer, or other sensor. The machine 700 may comprise an output controller 728, such as a serial (e.g., Universal Serial Bus (USB)), parallel, or other wired or wireless (e.g., infrared (IR), near field communication (NFC), etc.) connection, for communicating with or controlling one or more peripheral devices (e.g., a printer, a card reader, etc.).

[0096] The storage device 716 may comprise a machine-readable medium 722 on which is stored one or more sets of data structures or instructions 724 (e.g., software) that embody or are utilized by any one or more of the techniques or functions described herein. The instructions 724 may reside entirely, or at least partially, in the main memory 704, in the static memory 706, or in the hardware processor 702 during execution of the instructions 724 by the machine 700. In one example, one or any combination of the hardware processor 702, the main memory 704, the static memory 706, or the storage device 716 may constitute a machine-readable medium.

[0097] Although machine-readable medium 722 is illustrated as a single medium, the term “machine-readable medium” may include a single medium or multiple media (e.g., a central or distributed database, and / or associated caches and servers) configured to store one or more instructions 724.

[0098] The term "machine-readable medium" can include any medium capable of storing, encoding, or carrying instructions executed by the machine 700, causing the machine 700 to perform any one or more of the techniques of this disclosure, or capable of storing, encoding, or carrying data structures used by or related to such instructions. Non-limiting examples of machine-readable media can include solid-state memory and optical and magnetic media. In one example, a high-capacity machine-readable medium comprises a machine-readable medium that includes a plurality of particles having an unchanging (e.g., stationary) mass. Thus, a high-capacity machine-readable medium is not a transitory propagating signal. Specific examples of high-capacity machine-readable media can include non-volatile memory such as semiconductor memory devices (e.g., electrically programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EPSOM)) and flash memory devices, magnetic disks such as internal hard disks and removable disks, optical magnetic disks, and CD-ROM and DVD-ROM disks.

[0099] The instructions 724 may further be transmitted or received over a communications network 726 using a transmission medium via a network interface device 720 utilizing any of a number of transport protocols (e.g., Frame Relay, Internet Protocol (IP), Transmission Control Protocol (TCP), User Datagram Protocol (UDP), Hypertext Transfer Protocol (HTTP), etc.). Exemplary communications networks may include local area networks (LANs), wide area networks (WANs), packet data networks (e.g., the Internet), mobile telephone networks (e.g., cellular networks), Plain Old Telephone Service (POTS) networks, and wireless data networks (e.g., the Institute of Electrical and Electronics Engineers (IEEE) 802.11 family of standards known as WiFi®, the IEEE 802.16 family of standards known as WiMax®), the IEEE 802.15.4 family of standards, peer-to-peer (P2P) networks, among others. In one example, the network interface device 720 may include one or more physical jacks (e.g., Ethernet, coaxial, or phone jacks) or one or more antennas for connecting to the communications network 726. In one example, the network interface device 720 may be equipped with multiple antennas to communicate wirelessly using at least one of single-input multiple-output (SIMO), multiple-input multiple-output (MIMO), and multiple-input single-output (MISO) techniques. The term "transmission medium" shall be deemed to include any intangible medium capable of storing, encoding, or carrying instructions executed by the machine 700 and including digital or analog communication signals or other intangible media to facilitate communication of such software.

[0100] Additional Notes The above detailed description includes references to the accompanying drawings, which form a part of the detailed description. The drawings show, by way of example, specific embodiments in which the invention may be practiced. These embodiments are also referred to herein as "examples." Such examples may include elements in addition to those shown or described. However, the inventors also contemplate examples in which only the illustrated or described elements are provided. Furthermore, the inventors also contemplate examples that use any combination or permutation of the illustrated or described elements (or one or more aspects thereof) with respect to a particular example (or one or more aspects thereof) shown or described herein, or with respect to other examples (or one or more aspects thereof).

[0101] In this application, the terms "a" and "an" are used to include one or more, as is common in patent documents, independent of any other instances or usages of "at least one" or "one or more." In this application, the term "or" is used to refer to a non-exclusive, i.e., "A or B" includes "A but not B," "B but not A," and "A and B," unless otherwise specified. In this application, the terms "including" and "in which" are used as the plain English equivalents of the respective terms "comprising" and "wherein." Also, in the following claims, the terms "including" and "comprising" are open-ended; that is, a system, apparatus, article, or process that includes elements in addition to the elements recited after such terms in a claim is still considered to be within the scope of that claim. Moreover, in the following claims, the terms "first," "second," and "third," etc. are used merely as labels and are not intended to impose numerical requirements on their objects.

[0102] The above description is intended to be illustrative, not limiting. For example, the above examples (or one or more aspects thereof) can be used in combination with each other. Other embodiments may be used by those of ordinary skill in the art upon review of the above description. The Abstract is provided in compliance with 37 CFR § 1.72 to enable the reader to quickly ascertain the nature of the technical disclosure. The Abstract is submitted with the understanding that it will not be used to interpret or limit the scope or meaning of the claims. Also, in the above Detailed Description, various features may be grouped together to simplify the disclosure. This should not be construed as intending that an unclaimed disclosed feature is essential to any claim. Rather, inventive subject matter may lie in less than all features of a particular disclosed embodiment. Thus, the following claims are hereby incorporated into the Detailed Description as an example or embodiment, with each claim standing on its own as a separate embodiment, and it is contemplated that such embodiments can be combined with each other in various combinations or permutations. The scope of the present invention should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.

Claims

1. 1. A surgical system comprising: an electrosurgical or electromagnetic energy system configured to generate an electrosurgical or electromagnetic signal operable to ablate an anatomical target; a probe comprising an optical path configured to (i) pass the electrosurgical or electromagnetic signal to the anatomical target, and (ii) pass an optical signal from the anatomical target in response to illumination incident on the anatomical target; an optical splitter optically coupled to the probe, the optical splitter configured to direct the electrosurgical or electromagnetic signal to the optical path of the probe, receive at least a portion of the optical signal from the optical path of the probe, and redirect the at least a portion of the received optical signal; a temperature monitor coupled to at least one temperature sensor, the temperature monitor configured to monitor a temperature of the optical splitter in response to the emission of the electrosurgical or electromagnetic signal and to generate an over-temperature diagnosis of the optical splitter based at least in part on the monitored temperature; A surgical system comprising:

2. 10. The surgical system of claim 1, wherein the optical splitter further comprises a reflector having an aperture configured to allow the electrosurgical or electromagnetic signal to pass therethrough, and the at least one temperature sensor is substantially proximate to the aperture.

3. 10. The surgical system of claim 1, wherein the electrosurgical or electromagnetic energy system comprises a laser system configured to emit a laser pulse, and the temperature monitor is configured to synchronize temperature measurements with the laser pulse.

4. 2. The surgical system of claim 1, (i) the optical splitter further comprises a reflector; (ii) the at least one temperature sensor includes a temperature sensor on a non-reflective surface of the reflector; (iii) the temperature monitor is configured to detect a change in temperature of the non-reflective surface indicative of at least a portion of the electrosurgical or electromagnetic signal incident on the non-reflective surface of the reflector, and to generate the overheating diagnosis based at least in part on the detected change in temperature of the non-reflective surface.

5. 2. The surgical system of claim 1, (i) the optical splitter further comprises a reflector; (ii) the at least one temperature sensor includes a temperature sensor on a reflective surface of the reflector; (iii) the temperature monitor is configured to detect a change in temperature of the reflecting surface indicative of at least a portion of the electrosurgical or electromagnetic signal reflected from the anatomical target and incident on the reflective surface of the reflector, and to generate the overheating diagnosis based at least in part on the detected change in temperature of the reflective surface.

6. 2. The surgical system of claim 1, (i) the optical splitter further comprises a reflector; (ii) the at least one temperature sensor includes a first temperature sensor configured to sense a temperature of a non-reflective surface of the reflector opposite a reflective surface, and a second temperature sensor configured to sense a temperature of the reflective surface; (iii) the temperature monitor is configured to generate the overheating diagnosis based at least in part on a comparison of a temperature of the non-reflective surface to a temperature of the reflective surface.

7. 7. The surgical system of claim 6, wherein the overheating diagnosis comprises: a first indicator of misalignment between the probe and the optical splitter if the temperature of the reflective surface is greater than the temperature of the non-reflective surface; a second indicator of misalignment between the optical splitter and the electrosurgical or electromagnetic energy system if the temperature of the non-reflective surface is greater than the temperature of the reflective surface; and A surgical system comprising:

8. 10. The surgical system of claim 1, further comprising a controller circuit configured to generate control signals for adjusting settings of the electrosurgical or electromagnetic energy system based at least in part on the monitored temperature.

9. 1. A method of operating a surgical system including an optical splitter and a probe coupled to the optical splitter, comprising: The surgical system includes: directing an electrosurgical or electromagnetic signal through said optical splitter and said probe to an anatomical target; receiving at least a portion of an optical signal reflected from the anatomical target in response to illumination of the anatomical target; and configured to monitor a temperature of the optical splitter via a temperature sensor in response to the emission of the electrosurgical or electromagnetic signal; The method comprises: redirecting the at least a portion of the received optical signal through the optical splitter; monitoring a temperature of the optical splitter via the temperature sensor; generating an over-temperature diagnosis for the optical splitter based at least in part on the monitored temperature upon determining that the monitored temperature exceeds a predetermined threshold; A method for operating a surgical system comprising:

10. 10. The method of claim 9, wherein the electrosurgical or electromagnetic signal comprises a laser pulse, the method further comprising synchronizing the temperature monitoring with the laser pulse.

11. 10. A method of operating a surgical system according to claim 9, comprising: monitoring the temperature of the optical splitter includes detecting a temperature change of a reflector at the optical splitter, the temperature change being indicative of at least a portion of the electrosurgical or electromagnetic signal incident on the reflector; A method of operating a surgical system, wherein generating the overheating diagnosis is based at least in part on the detected temperature change.

12. 12. The method of claim 11, wherein detecting the temperature change of the reflector includes detecting a temperature change in at least one of a reflective surface or a non-reflective surface of the optical splitter.

13. 10. A method of operating a surgical system according to claim 9, comprising: monitoring the temperature of the optical splitter includes detecting a first temperature of a non-reflective surface of a reflector of the optical splitter and detecting a second temperature of a reflective surface of the reflector opposite the non-reflective surface; A method of operating a surgical system, wherein generating the overtemperature diagnosis is based at least in part on a comparison of the first temperature and the second temperature.

14. 14. The method of claim 13, wherein the overheat diagnosis comprises: a first indicator of misalignment between the optical splitter and the probe if the second temperature is greater than the first temperature; and a second indicator of misalignment between the optical splitter and an electrosurgical or electromagnetic energy system generating the electrosurgical or electromagnetic signal if the first temperature is greater than the second temperature; and A method for operating a surgical system comprising:

15. 10. The method of claim 9, wherein the electrosurgical or electromagnetic signal is generated by an electrosurgical or electromagnetic energy system, the method further comprising adjusting settings of the electrosurgical or electromagnetic energy system based at least in part on the monitored temperature.

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