US20090012511A1

US20090012511A1 - Surgical waveguide

Info

Publication number: US20090012511A1
Application number: US12/135,968
Authority: US
Inventors: Richard Shaun Welches; James Henry Boll
Original assignee: Cynosure LLC
Current assignee: Cynosure LLC
Priority date: 2007-06-08
Filing date: 2008-06-09
Publication date: 2009-01-08
Also published as: EP2155333A1; EP2155333A4; EP2158516A1; EP2155098A4; WO2008153999A1; KR20100039330A; KR20100029235A; EP2155100A4; US20090024023A1; US20090018531A1; EP2155100A1; US8190243B2; KR20100041753A; EP2158508A1; KR20100039332A; US20110264083A1; WO2008154006A1; WO2008154005A1; WO2008154000A1; US20120253222A1

Abstract

A surgical probe is disclosed which includes a stiff treatment waveguide extending between a first end and a second end, the first end being adapted for connection to a handpiece, the second end being adapted for insertion through an incision into an area of tissue. The treatment waveguide in configured to receive treatment light from the handpiece at the first end, transmit the light to the second end, and emit the light from the second end into a portion of the tissue proximal the second end. The treatment waveguide is adapted to penetrate through a portion of the area of tissue in response to pressure applied to the handpiece.

Description

CROSS REFERENCE TO RELATED APPLICATIONS

The present application claims benefit to each of U.S. Provisional Application Ser. No. 60/987,596, filed Nov. 13, 2007, U.S. Provisional Application Ser. No. 60/987,617, filed Nov. 13, 2007, U.S. Provisional Application Ser. No. 60/987,819, filed Nov. 14, 2007, U.S. Provisional Application Ser. No. 60/987,821, filed Nov. 14, 2007, U.S. Provisional Application Ser. No. 61/018,727, filed Jan. 3, 2008, U.S. Provisional Application Ser. No. 61/018,729, filed Jan. 3, 2008, and U.S. Provisional Application Ser. No. 60/933,736, filed Jun. 8, 2007, the contents each of which are incorporated by reference herein in their entirety.

BACKGROUND

The present invention relates to a surgical waveguide. Plastic surgeons, dermatologists, and their patients continually search for new and improved methods for treating the effects of an aging or otherwise damaged skin. One common procedure for rejuvenating the appearance of aged or photodamaged skin is laser skin resurfacing using a carbon dioxide laser. Another technique is non-ablative laser skin tightening, which does not take the top layer of skin off, but instead uses a deep-penetrating laser to treat the layers of skin beneath the outer epidermal layer, tightening the skin and reducing wrinkles to provide a more youthful appearance.
For such techniques as laser skin tightening treatment, it has been difficult to control the depth and amount of energy delivered to the collagen without also damaging or killing the dermal cells. Much of the energy of the treatment pulse is wasted due to scattering and absorption in the outer epidermal layer, and the relatively high pulse energy required to penetrate this outer layer can cause pain and epidermal damage.
Some skin tightening techniques include using a hollow tubular cannula that contains an optical fiber connected to a laser source. The cannula can be inserted subcutaneously into a patient so that the end of the fiber is located within the tissue underlying the dermis. The source emits a treatment output, for example an output pulse that is conveyed by the fiber to the dermis, which causes collagen shrinkage within the treatment area, thus tightening the skin.
A technical complication common to the use of cannula sheathed optical fibers for surgical applications is the break off of fatigued fiber ends (‘tips’). Additionally, an improperly tightened optical fiber can slide up into the cannula such that the fiber tip is located within the cannula air space. This can cause very high cannula and fiber tip temperatures with corresponding excessive temperatures coupled to adjacent tissue. The susceptibility of standard optical fibers to tip breakage is worsened by autoclave cycles and by long duration high power use.

SUMMARY OF THE INVENTION

In one aspect, the inventors have realized that a surgery tool employing a robust waveguide can be used in an invasive laser surgical procedure. Use of such a waveguide can eliminate the need for a cannula, as the waveguide may be inserted directly into the incision. This improves both safety and efficacy in that broken and lost optical fiber tips are avoided. Further, this reduces or eliminates the possibility of the waveguide slipping up into a cannula or catheter and operating within an air filled space in the cannula or catheter, leading to excessive waveguide tip temperature rise.
In another aspect, the inventors have realized that including infrared (IR) temperature sensing with a laser surgical device of the type described above, or otherwise, allows for temperature monitoring of a treatment area. Temperature information can be used as a feedback to control the applied treatment.
In some embodiments, a surgery tool or a surgical probe includes a stiff treatment waveguide extending between a first end and a second end, the first end being adapted for connection to a handpiece, and the second end being adapted for insertion through an incision into an area of tissue. In some embodiments, the treatment waveguide is configured to receive treatment light from the handpiece at the first end, transmit the light to the second end, and emit the light from the second end into a portion of the tissue proximal the second end.
In some embodiments, the treatment waveguide is adapted to penetrate through a portion of the area of tissue in response to pressure applied to the handpiece. In some embodiments, the treatment waveguide is substantially free of external mechanical support. The treatment waveguide is free from an external cannula.
In some embodiments, the treatment waveguide includes an optical fiber having a diameter of about 1000 μm to about 2000 μm. The treatment waveguide may be composed of one or more materials selected from the list of: glass, plastic, quartz, and Nd glass, and a Cerium-doped quartz. A treatment waveguide composed of a glass may be sheathed in a plastic coating to prevent fragments and shards from an accidental break from contaminating a treatment site.
In some embodiments, the surgical probe of the sensing waveguide is adapted to transmit treatment light at wavelengths of about 532 nm to about 1550 nm. The second end of the treatment waveguide comprises a strip and cleave tip. The second end of the treatment waveguide comprises one selected from the group of: a wedge shaped tip, an angled tip, or a side firing tip.
In some embodiments, the first end of the treatment waveguide is adapted for detachable connection to the handpiece. In some embodiments, the handpiece itself includes one or more optical elements adapted to direct light from a light source to the first end of the treatment waveguide. The handpiece may further include: a sterile sheath defining an interior volume and an exterior volume, where the one or more optical elements are positioned within the interior volume and the treatment waveguide is positioned in the exterior volume, and a connector adapted to receive the first end of the treatment waveguide and to optically couple first end of the treatment waveguide to the one or more optical elements while preventing pneumatic communication between the interior and exterior volumes.
In some embodiments, the treatment waveguide is adapted to receive infrared light from an area of tissue proximal the second end of the sensing waveguide, direct the infrared light to the first end of the sensing waveguide, and emit the infrared light onto a infrared temperature sensor located within the handpiece.
In some embodiments, the surgical probe further includes a sensing waveguide extending between a first end proximal the first end of the treatment waveguide and a second end proximal the second end of the treatment waveguide, where the waveguide is adapted to receive infrared light from an area of tissue proximal the second end of the sensing waveguide, direct the infrared light to the first end of the sensing waveguide, and emit the infrared light onto a infrared temperature sensor located within the handpiece.
In some embodiments, the surgical probe sensing waveguide is coaxial with the treatment waveguide. In some embodiments, the sensing waveguide comprises an optical fiber positioned beside the treatment waveguide. In some embodiments, the sensing waveguide is relatively less stiff than the treatment waveguide, and further includes an overjacket surrounding the treatment waveguide and the sensing waveguide adapted to secure the treatment waveguide and the sensing waveguide in fixed relative position. The sensing waveguide is adapted to transmit light at wavelengths of about 5 μm to about 14 μm. The treatment waveguide may be composed of ZnSe.
In some embodiments, the surgical probe further includes: the handpiece, the temperature sensor, and a processor, where the temperature sensor is configured to detect one or more properties of the infrared light from the first end of the sensing waveguide, and where the processor is configured to determine information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the one or more detected properties of the light.
In some embodiments, the surgical probe further includes an optical element configured to separate a first portion of the infrared light at a first wavelength and a second portion of the infrared light at a second wavelength, where the temperature sensor is configured to detect a property of the first portion and a property of the second portion, and the processor is configured to determine information indicative of the temperature of the area of tissue proximal the second end of the sensing waveguide based on the property of the first portion and the property of the second portion.
In some embodiments, the processor is configured to determine information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the property of the first portion and the property of the second portion by comparing the properties. In some embodiments, the processor is configured to control the treatment light based on the determined information indicative of the temperature of the area of tissue.
In some embodiments, a method is defined including: providing a stiff treatment waveguide extending between a first end and a second end, the first end connected to a handpiece, the second end being adapted for insertion through an incision into an area of tissue, where the treatment waveguide being substantially free of external mechanical support. The method further includes: inserting said waveguide into an incision in a patient, applying pressure to the handpiece to advancing said waveguide through an area of tissue, providing treatment light directed from a treatment source to the handpiece, directing treatment light to the first end of the treatment waveguide, transmitting the light from the first end to the second end, and emitting the light from the second end into a portion of tissue proximal the second end.
In some embodiments, the method may specify the treatment waveguide is free from an external cannula. The method further may include: repetitively advancing and withdrawing the treatment waveguide along multiple paths through the area of tissue and applying treatment light to multiple areas of tissue along the multiple paths. The method may further include: providing a sensing waveguide extending between a first end proximal the first end of the treatment waveguide and a second end proximal the second end of the treatment waveguide, receiving infrared light from an area of tissue proximal the second end of the sensing waveguide, directing the infrared light to the first end of the sensing waveguide, and emitting the infrared light onto a infrared temperature sensor located within the hand piece.
In some embodiments, using the temperature sensor, the method may further specify detecting one or more properties of the infrared light from the first end of the sensing waveguide and determining information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the one or more detected properties of the light. In some embodiments, the method further includes controlling application of the treatment light based on the determined information indicative of the temperature of the area of tissue.

BRIEF DESCRIPTION OF THE DRAWINGS

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

FIG. 1 shows a first view of a surgical waveguide

FIG. 2 shows a second view of a surgical waveguide.

FIG. 3 shows an partial assembly drawing of a surgical waveguide.

FIG. 4 shows an assembly drawing of a connection between the surgical waveguide and an optics focus interface to a fiber optic line.

FIG. 5 shows a collection of surgical waveguide tips designs.

FIG. 6 shows a surgical waveguide integrated with a thermal temperature sensor.

FIG. 7 shows a cross sectional view of the optics focus interface between the surgical waveguide and a fiber optic line.

FIG. 8 shows a plot of radiation transmission vs. wavelength for a ZnSe sense fiber with an anti-reflection (AR) coating.

DETAILED DESCRIPTION

FIGS. 1 and 2 show a first and a second view of a surgical waveguide adapted for use in a subdermal tissue ablation procedure according to an embodiment. FIGS. 1 and 2 show a laser surgical waveguide assembly 100 including a hand piece 105 which receives a surgical waveguide 110. The surgical waveguide 110 is chosen to have suitable mechanical, material, and optical properties for surgical applications without need for a supporting cannula. That is, the surgical waveguide 110 itself may be inserted through an incision directly into a patient's tissue for the delivery of therapeutic laser light. For example, the waveguide may be chosen to be mechanically strong and/or stiff enough to withstand multiple aggressive passes into fibrous tissue, while being capable of transmitting high power laser pulses. Further, the waveguide may be chosen to be mechanically strong and/or stiff enough to maintain control of a surgical waveguide 110 tip, such that the surgical waveguide 110 body undergoes a minimum of flexure under a compressive or shear force applied by the hand piece 105. In some embodiments, the waveguide may be removable, disposable, and/or consumable
For example, in some embodiments, the surgical waveguide 110 can be a relatively short (e.g., about 6″ or less) length of large core fiber having a large diameter (e.g. about 1000 μm or more, about 1000-2000 μm, or greater than 2000 μm. The cost for such a fiber is low due to the short fiber length, but due to its large diameter, the fiber has sufficient mechanical strength to meet the requirements of surgical applications. The larger diameter of the fiber at the fiber tip lowers the power density at the tip and may add to the longevity of the fiber tip. In some embodiments, the surgical waveguide is a consumable, large diameter, (e.g., 1800 μm) optical fiber with a strip and cleave tip. In such embodiments, as the tip of the fiber becomes worn with use, it may be removed, and the exposed fiber end may be cleaved to provide a new operating tip.
In some embodiments, the surgical waveguide 110 comprises a stiff glass or plastic waveguide suitable for surgical applications without the need for a cannula. Other suitable waveguide materials include glass or quartz rods with some sort of cladding, hollow tubing with dielectric coatings, Nd glass, and Cerium-doped quartz. In some embodiments, waveguides made of glass are sheathed in a plastic coating analogous to a safety glass to retain glass fragments and shards within the plastic coating if the glass breaks, and greatly reducing the possibility of glass fragments and shards contaminating a treatment site. In various embodiments, the surgical waveguide 110 requires a cladding material. The cladding material may be selected to add necessary strength and stiffness to the surgical waveguide 110, eliminating the need for cannula. Although several examples of waveguide types have been provided, it is to be understood by those skilled in the art that any other suitable material or configuration may be used.
Referring again to FIG. 1, the surgical waveguide 110 is held in place in the hand piece 105 by a waveguide chuck 115. The surgical waveguide 110 protrudes from the back end of the hand piece 105 and is received by a waveguide stop 120. A treatment laser light from a treatment laser 450 is coupled to a reusable optical fiber 125 which terminates in a connector 130, for example, an SMA-like connector, which receives the hand piece 105.
Light from the reusable optical fiber 125 is coupled into the surgical waveguide 110 using a focusing assembly 135 including, for example, a set of optical elements 140. The set of optical elements 140 includes, for example, lenses, a single or dual focus mirror, and others. The set of optical elements 140 directs light from the end of the reusable fiber 125 into the surgical waveguide 110. In some embodiments, an optical coupling can be achieved by placing the end faces of the reusable fiber 125 and the surgical waveguide 110 in contact or close proximity, a technique known as ‘butt-splicing’. Note that, because the reusable fiber 125 is not inserted into the patient, the reusable fiber 125 need not be as physically strong as the surgical waveguide 110. For example, in some embodiments, the reusable fiber may be a 300-600 μm fiber.
The surgical waveguide 110 and hand piece 105 may be sterilized using, for example, an autoclave. The reusable fiber 125, connector 130, and focusing assembly 135 are covered with a sterile sheath 150, and thus need not be autoclaved. Note that this allows for the use of, for example, a focusing assembly 135 including optical elements 140 that are not sufficiently robust to undergo one or more autoclave cycles.
FIG. 3 shows a partial assembly drawing of a surgical waveguide adapted for use in a subdermal tissue ablation procedure according to an embodiment. FIG. 4 shows an assembly drawing of a connection between the surgical waveguide and an optics focus interface to a fiber optic line according to an embodiment. When connected, the surgical waveguide 110 pierces through the sterile sheath 150. The sterile sheath 150 is clamped between the hand piece 110 and the connector 130, thereby maintaining the integrity of the sheath. For example, in some embodiments the hand piece 110 may include a coupling with an O-ring groove 305. The connector 130 and focus assembly 135 may include a matching O-ring 310. When connected, the O-ring 310 compresses the sterile sheath 150 against the hand piece 110 O-ring groove 305, preventing communication between the sterile region inside the sterile sheath 150 and the non-sterile region outside of the sterile sheath 150.
FIG. 5 shows a collection of surgical waveguide tips designs according to an embodiment. FIG. 5 shows several embodiments of surgical waveguides, including a glass waveguide 505, a consumable optical fiber 510 with strip and cleave end as described above, a hollow metal waveguide 515, and a quartz waveguide 520. A collection of waveguide tips with different exemplary configurations are shown, whereby arrows indicate the direction of light emission. The collection of waveguide tips includes: wedge tips 550, angled tips 555, and side-firing tips 560. In some embodiments, the surgical waveguide 110 may be discarded after each use. In some embodiments, the surgical waveguide 110 may be reused multiple times, for example, being sterilized by autoclave between each use. In some embodiments, the surgical waveguide 110 may be discarded after a given number of uses, duration of use, duration of use at a given power level, etc.
FIG. 6 shows the surgical waveguide integrated with an IR temperature sensor adjacent to the treatment waveguide fiber tip. FIG. 7 shows a cross sectional view of the optics focus interface between the surgical waveguide and a fiber optic line. An IR waveguide 605, for example a ZnSe sense fiber, is bundled with the surgical waveguide 110 in an over-jacket 610. In the example shown, a two sensor IR photodetector assembly 615 is located in the hand piece 105 adjacent to the treatment beam focus assembly 135. Portions of light from the IR waveguide 605 at two distinct wavelengths are separated and directed respectively to the two IR sensors 620 using, for example, a dichroic beamsplitter 621. Signals from the two IR sensors 620 are compared differentially to increase sensitivity and reject errors due to a sense waveguide 605 transmission loss variables or characteristics.
The signals from the two IR sensors 620 are processed to obtain temperature information about a tissue under treatment. IR temperature monitoring provides a tissue temperature feedback to the treatment laser 450, which may use the tissue temperature feedback to adjust laser energy deposition based on observed tissue temperatures. In various embodiments, adjusting laser energy deposition could include a simple maximum temperature safety limit, or the tissue temperature feedback could allow for a closed loop tissue temperature control. In either case, the treatment laser 450 takes feedback from the IR sense fiber 605, or equivalently, from an IR sense fiber ring 705, then adjusts the treatment laser 450 output power in a closed loop to achieve a selected tissue temperature.
In some embodiments, the surgical waveguide itself can collect IR light from the treatment area during treatment to provide IR tissue temperature sensing. However, for some applications, such a waveguide or fiber would be required to pass high energy treatment laser 450 wavelengths in the range of approximately 532 to 1550 nm and also to pass IR wavelengths on the order of 5-14 μm for temperature sensing and feedback. In some embodiments, this may be an unwanted requirement. Referring back to FIG. 6 shows an example of a device which avoids this requirement by employing a dual fiber approach.
As with the systems described above, light at a treatment wavelength is delivered via a surgical waveguide 110, for example, a stiffened fiber suitable for surgical use without a cannula. As shown in FIG. 7, the surgical waveguide 110 is surrounded by and coaxial with an IR waveguide tube 710, as an example, a ZnSe sense fiber cylinder or tube. As described above, the surgical waveguide 110 is coupled to a treatment fiber 125 which delivers light from a treatment source, in the given example, a treatment laser 450 source. The coupling is accomplished using a focus assembly 135 in a connector 130 connected to the back of the hand piece 105. As shown in FIG. 7, the connector 130 also includes an IR pass filter ring 715 to filter out stray treatment laser 450 light and an IR sense fiber ring 705, as an example, an annular array of IR photodetectors, aligned with the IR waveguide tube 710. The IR sense fiber ring 705 produces electrical signals in response to incident IR radiation. The electrical signals corresponding to IR radiation incident to the IR sense fiber ring 705 are directed to a processor 706, which functions to determine the tissue temperature and to provide a feedback to the treatment laser 450, as described above.
As described above, in various embodiments, IR radiation from a treatment site is propagated to an IR photodetector assembly 615 through the IR pass filter ring 715 via the IR sense fiber ring 705 and IR waveguide tube 710, or via other suitable optics. Other optics suitable to function as the IR waveguide tube 710 may include, for example, anti-reflection (AR) coated ZnSe or Germanium rods or tubes, or certain IR transmissive plastics, or even photonic waveguides. FIG. 8 shows a plot of radiation transmission vs. wavelength 800 for a ZnSe sense fiber with an anti-reflection (AR) coating as implemented.
Although several examples of IR optics and geometries are presented, it is to be understood that other suitable materials, geometries, and configurations may be used.
While this invention has been particularly shown and described with references to example embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the invention.
For example, it is to be understood that although in the examples provided above laser light is used for treatment, other sources of treatment light (e.g. flash lamps, light emitting diodes) may be used.
In some embodiments, a safety accelerometer 160 may be incorporated in the laser surgical waveguide assembly 100. For example, as shown in FIGS. 1 and 2, an accelerometer 160 may by included within the sterile sheath 150 and attached to, for example, the connector 130 or focus assembly 135. The accelerometer 160 may be attached to, for example, an electronic processor 706 via wiring 161 contained in the sterile sheath 150. During treatment, the accelerometer 160 measures acceleration of the hand piece 105 and may determine, for example, if the hand piece 105 has come to rest in a single position for too long a period of time, potentially leading to unsafe heating levels, triggering, for example, a warning, or treatment laser 450 shut off.
In various embodiments, other safety devices (e.g. position sensors, temperature sensors, etc.) may similarly be incorporated with the surgical waveguide 110 and hand piece 105.
One or more or any part thereof of the treatment, IR sensing, or safety techniques described above can be implemented in computer hardware or software, or a combination of both. The methods can be implemented in computer programs using standard programming techniques following the method and figures described herein. Program code is applied to input data to perform the functions described herein and generate output information. The output information is applied to one or more output devices such as a display monitor. Each program may be implemented in a high level procedural or object oriented programming language to communicate with a computer system. However, the programs can be implemented in assembly or machine language, if desired. In any case, the language can be a compiled or interpreted language. Moreover, the program can run on dedicated integrated circuits preprogrammed for that purpose.
Each such computer program is preferably stored on a storage medium or device (e.g., ROM or magnetic diskette) readable by a general or special purpose programmable computer, for configuring and operating the computer when the storage media or device is read by the computer to perform the procedures described herein. The computer program can also reside in cache or main memory during program execution. The analysis method can also be implemented as a computer-readable storage medium, configured with a computer program, where the storage medium so configured causes a computer to operate in a specific and predefined manner to perform the functions described herein.
As used herein the term “light” is to be understood to include electromagnetic radiation both within and outside of the visible spectrum, including, for example, ultraviolet and infrared radiation.
While the invention has been described in connection with the specific embodiments thereof, it will be understood that it is capable of further modification. Furthermore, this application is intended to cover any variations, uses, or adaptations of the invention, including such departures from the present disclosure as come within known or customary practice in the art to which the invention pertains, and as fall within the scope of the appended claims.
It should be appreciated that the particular implementations shown and described herein are examples and are not intended to otherwise limit the scope in any way.

Claims

1. A surgical probe comprising:

a stiff treatment waveguide extending between a first end and a second end, said first end being adapted for connection to a handpiece, said second end being adapted for insertion through an incision into an area of tissue;

wherein said treatment waveguide in configured to receive treatment light from the handpiece at the first end, transmit the light to the second end, and emit the light from the second end into a portion of the tissue proximal the second end; and

wherein the treatment waveguide is adapted to penetrate through a portion of the area of tissue in response to pressure applied to the handpiece.

2. The surgical probe of claim 1, wherein the treatment waveguide is substantially free of external mechanical support.

3. The surgical probe of claim 2, wherein the treatment waveguide is free from an external cannula.

4. The surgical probe of claim 3, wherein the treatment waveguide comprises an optical fiber having a diameter of about 1000 μm to about 2000 μm.

5. The surgical probe of claim 4, wherein the treatment waveguide comprises one or more selected from the list of: glass, plastic, and quartz.

6. The surgical probe of claim 3, wherein the sensing waveguide is adapted to transmit treatment light at wavelengths of about 532 nm to about 1550 nm.

7. The surgical probe of claim 3, wherein the second end of the treatment waveguide comprises a strip and cleave tip.

8. The surgical probe of claim 3, wherein the second end of the treatment waveguide comprises one selected from the group of: a wedge shaped tip, an angled tip, or a side firing tip.

9. The surgical probe of claim 3, wherein said first end of the treatment waveguide is adapted for detachable connection to the handpiece.

10. The surgical probe of claim 9, further comprising the handpiece, wherein the handpiece comprises one or more optical elements adapted to direct light from a light source to the first end of the treatment waveguide.

11. The surgical probe of claim 10, wherein the handpiece comprises

a sterile sheath defining an interior volume and an exterior volume, wherein said one or more optical elements are positioned within the interior volume and the treatment waveguide is positioned in the exterior volume; and

a connector adapted to receive the first end of the treatment waveguide and to optically couple first end of the treatment waveguide to the one or more optical elements while preventing pneumatic communication between the interior and exterior volumes.

12. The surgical probe of claim 3, wherein the treatment waveguide is adapted to receive infrared light from an area of tissue proximal the second end of the sensing waveguide, direct the infrared light to the first end of the sensing waveguide, and emit the infrared light onto a infrared temperature sensor located within the handpiece.

13. The surgical probe of claim 3, further comprising

a sensing waveguide extending between a first end proximal the first end of the treatment waveguide and a second end proximal the second end of the treatment waveguide;

wherein said waveguide is adapted to receive infrared light from an area of tissue proximal the second end of the sensing waveguide, direct the infrared light to the first end of the sensing waveguide, and emit the infrared light onto a infrared temperature sensor located within the handpiece.

14. The surgical probe of claim 13, wherein the sensing waveguide is coaxial with the treatment waveguide.

15. The surgical probe of claim 13, wherein the sensing waveguide comprises an optical fiber positioned beside the treatment waveguide.

16. The surgical probe of claim 15, wherein the sensing waveguide is relatively less stiff than the treatment waveguide, and further comprising an overjacket surrounding the treatment waveguide and the sensing waveguide adapted to secure the treatment waveguide and the sensing waveguide in fixed relative position.

17. The surgical probe of claim 13, wherein the sensing waveguide is adapted to transmit light at wavelengths of about 5 μm to about 14 μm.

18. The surgical probe of claim 13, wherein the treatment waveguide comprises ZnSe.

19. The surgical probe of claim 13, further comprising:

the handpiece;

the temperature sensor; and

a processor,

wherein the temperature sensor is configured to detect one or more properties of the infrared light from the first end of the sensing waveguide, and wherein the processor is configure to determine information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the one or more detected properties of the light.

20. The surgical probe of claim 19. further comprising the an optical element configured to separate a first portion of the infrared light at a first wavelength and a second portion of the infrared light at a second wavelength;

wherein the temperature sensor is configured to detect a property of the first portion and a property of the second portion; and

wherein the processor is configured to determine information indicative of the temperature of the area of tissue proximal the second end of the sensing waveguide based on the property of the first portion and the property of the second portion.

21. The surgical probe of claim 20, wherein the processor is configured to determine information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the property of the first portion and the property of the second portion by comparing the properties.

22. The surgical probe of claim 19, wherein the processor is configured to control the treatment light based on the determined information indicative of the temperature of the area of tissue.

23. A method comprising:

providing a stiff treatment waveguide extending between a first end and a second end, said first end connected to a handpiece, said second end being adapted for insertion through an incision into an area of tissue, said treatment waveguide being substantially free of external mechanical support;

inserting said waveguide into an incision in a patient;

applying pressure to the handpiece to advancing said waveguide through an area of tissue;

providing treatment light directed from a treatment source to the handpiece

directing treatment light to the first end of the treatment waveguide,

transmitting the light from the first end to the second end,

emitting the light from the second end into a portion of tissue proximal the second end.

24. The method of claim 23, wherein the treatment waveguide is free from an external cannula.

25. The method of claim 24, further comprising:

repetitively advancing and withdrawing the treatment waveguide along multiple paths through the area of tissue;

applying treatment light to multiple areas of tissue along the multiple paths.

26. The method of claim 25, further comprising:

providing sensing waveguide extending between a first end proximal the first end of the treatment waveguide and a second end proximal the second end of the treatment waveguide,

receiving infrared light from an area of tissue proximal the second end of the sensing waveguide;

directing the infrared light to the first end of the sensing waveguide,

emitting the infrared light onto a infrared temperature sensor located within the handpiece;

using the temperature sensor, detecting one or more properties of the infrared light from the first end of the sensing waveguide, and

determine information indicative of the temperature of the tissue area of tissue proximal the second end of the sensing waveguide based on the one or more detected properties of the light.

27. The method of claim 26, further comprising, controlling application of the treatment light based on the determined information indicative of the temperature of the area of tissue.