US20180243032A1

US20180243032A1 - Side-firing fiber delivery device with active cooling cap

Info

Publication number: US20180243032A1
Application number: US15/964,330
Authority: US
Inventors: Yihlih Peng; Gerald M. Mitchell
Original assignee: Boston Scientific Scimed Inc
Current assignee: American Medical Systems LLC; Boston Scientific Scimed Inc
Priority date: 2007-08-03
Filing date: 2018-04-27
Publication date: 2018-08-30
Also published as: US20150011985A1; US9980776B2; US9456871B2; US20090048588A1; US20160367320A1; US8858542B2

Abstract

A medical laser system and related methods of utilizing cooling within and around an optical fiber tip to prevent premature failure of the optical fiber. The optical fiber is surrounded by protective jacket assembly including a body tube assembly and a tip cap assembly. The body tube assembly includes an internal fiber jacket and an external body tube with a body tube channel defined therebetween. The tip cap assembly includes an inner cap member and an outer cap member defining a cap irrigation channel therebetween. Together, the cap irrigation channel and body tube channel cooperatively define an internal irrigation channel. The optical fiber can be delivered to a treatment location through a cystoscope. Saline is directed through an external irrigation channel between the cystoscope and the protective jacket assembly as well as the internal irrigation channel to cool the fiber tip and prevent overheating and failure of the optical fiber.

Description

PRIORITY CLAIM

The present application claims priority to U.S. Provisional Application Serial No. 60/953,721 filed Aug. 3, 2007, and entitled “Side-Firing Fiber Delivery Device with Active Cooling Cap”, which is hereby incorporated by reference in its entirety.

FIELD OF THE INVENTION

This invention relates to the field of medical lasers utilizing optical fibers. More specifically, the present invention relates to a side-firing optical fiber utilizing internal and external cooling streams to prevent premature failure at a fiber tip.

BACKGROUND OF THE INVENTION

Medical lasers have been used in treatment procedures involving various practice areas, including, for example, urology, neurology, otorhinolaryngology, general anesthetic ophthalmology, dentistry, gastroenterology, cardiology, gynecology, and thoracic and orthopedic procedures. Generally, these procedures require precisely controlled delivery of laser energy, and often the area to which the laser energy is to be delivered is located deep within the body; for example, at the prostate or at the fallopian tubes. Due to the location of the target tissue deep within the body, the medical procedure requires that the optical fiber be flexible and maneuverable. Various light sources can be used with optical fiber devices dependent upon the requirements for the light source; for example, pulsed lasers, diode lasers and neodymium lasers can be used as light sources. Representative lasers used in medical treatment procedures include Ho:YAG lasers and Nd:YAG lasers.
In medical procedures utilizing laser energy, the laser is coupled to an optical fiber adapted to direct laser radiation from the laser, through the fiber and to the treatment area. Typically, a surgical probe is utilized in the treatment of body tissue with laser energy. The surgical probe generally includes an optical fiber coupled to a laser source, and the probe tip is positioned on the optical fiber opposite the laser source, such that the tip of the probe can be positioned adjacent to the targeted tissue. Laser energy is directed out of the probe tip of the optical fiber onto desired portions of the targeted tissue.
Depending upon the operational conditions during laser treatment, a cap on the surgical probe can overheat. Overheating of the cap can lead to failure of the optical fiber. If the optical fiber fails, the laser system fails. Overheating of the cap can cause the cap to burn, detach, or even shatter during treatment inside the patient, which can lead to injury to the patient.

SUMMARY OF THE INVENTION

The present invention comprises a medical laser system and related methods of utilizing cooling within and around an optical fiber tip so as to prevent premature failure of the optical fiber. The optical fiber comprises an internal fiber jacket having a fiber tip for directing laser energy from the optical fiber. The optical fiber is generally surrounded by a body tube and a tip cap assembly. The tip cap assembly generally comprises an inner cap member and an outer cap member. The outer cap member includes a side port positioned within an exterior surface. An internal irrigating channel is defined between the inner cap member and the outer cap member. The optical fiber is generally configured for insertion through a cystoscope such that the fiber tip can be positioned proximate a treatment location. Once the fiber tip is properly positioned, saline can be directed through the irrigating channel as well as between the cystoscope and the exterior surface to cool the optical fiber and prevent overheating and subsequent failure of the optical fiber. In addition, the use of the outer cap member provides a barrier between the fiber tip and treatment location so as to prevent adhesion of ablated tissue to the fiber tip.
In one aspect, the present invention is directed to an optical fiber having a tip cap assembly defining an internal irrigation channel. The optical fiber can be configured for insertion into a cystoscope wherein saline can be simultaneously directed through the internal irrigation channel and between the cystocope and an exterior surface of the tip cap assembly. By continually circulating saline both internally and externally of the fiber tip, overheating of the fiber tip is prevented so as to prevent premature failure of the optical fiber.
In another aspect, the present invention is directed to a method for preventing overheating of an optical fiber. The method comprises providing an optical fiber having an internal irrigation channel at a fiber tip. The method further comprises circulating saline through the internal irrigation channel to remove heat energy from the fiber tip. The method further comprises circulating a cooling saline between a cystoscope and an exterior surface of the fiber tip. The method can further comprise providing a physical barrier between a discharge portion of the optical fiber and the treatment location to prevent adhesion of ablated tissue to the optical fiber.
In yet another aspect, the present invention is directed to a medical laser treatment system comprising a laser unit and an optical fiber capable of being introduced to a treatment location with a cystoscope. A fiber tip of the optical fiber is capable of being cooled simultaneously with an external cooling stream between the cystoscope and protective jacket assembly as well as through an internal irrigation channel defined by a tip cap assembly.
The above summary of the various representative embodiments of the invention is not intended to describe each illustrated embodiment or every implementation of the invention. Rather, the embodiments are chosen and described so that others skilled in the art may appreciate and understand the principles and practices of the invention. The figures in the detailed description that follows more particularly exemplify these embodiments.

BRIEF DESCRIPTION OF THE DRAWINGS

These as well as other objects and advantages of this invention, will be more completely understood and appreciated by referring to the following more detailed description of the presently preferred exemplary embodiments of the invention in conjunction with the accompanying drawings of which:

FIG. 1 is a block diagram illustration of a laser system according to an embodiment of the present invention.

FIG. 2 is a perspective end view of an optical fiber according to an embodiment of the present invention.

FIG. 3 is a section view of the optical fiber of FIG. 2.

FIG. 4 is a section view of the optical fiber of FIG. 2 being introduced to a treatment location with a cystoscope according to an embodiment of the present invention.

FIG. 5 is a graph comparing percentage of transmission of a optical fiber (2090 fiber) to an optical fiber with active cooling cap of the present invention.

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

DETAILED DESCRIPTION OF THE DRAWINGS

The present invention comprises an optical fiber for use with a medical laser system that utilizes internal and external cooling streams and related methods of monitoring an optical fibers to determine if an optical fiber cap on the optical fiber is in imminent danger of cap failure. The laser system includes a photodetector for converting returned light from the optical fiber cap to an electronic signal for comparison to a trigger threshold value known to be indicative imminent fiber cap failure. The returned light can be the main laser treatment wavelength, an auxiliary wavelength such as an aiming beam or infrared wavelengths generated by a temperature of the optical fiber cap. In the event the electronic signal reaches the trigger threshold value, the laser system can be temporarily shut-off or the power output can be reduced. In one preferred embodiment, the present invention can be utilized as part of a Greenlight HPS system manufactured by American Medical Systems of Minnetonka, Minn. and as described in U.S. Pat. Nos. 6,554,824 and 6,986,764, which are herein incorporated by reference.
Referring to FIG. 1, there is depicted a block diagram showing an exemplary laser system 100 which may be employed for implementing the present invention. Laser system 100 includes a solid-state laser unit 102, which is used to generate laser light for delivery through optical fiber 106 to target tissue 104. Laser unit 102 is capable of being operated in a pulsed mode or continuous wave.
Laser unit 102 more specifically comprises a laser element assembly 110, pump source 112, and frequency doubling crystal 122. In the preferred-embodiment, laser element 110 outputs 1064 nm light which is focused into frequency doubling crystal 122 to create 532 nm light. According to one implementation, laser element assembly 110 may be neodymium doped YAG (Nd:YAG) crystal, which emits light having a wavelength of 1064 nm (infrared light) when excited by pump source 112. Laser element 110 may alternatively be fabricated from any suitable material wherein transition and lanthanide metal ions are disposed within a crystalline host (such as YAG, Lithium Yttrium Fluoride, Sapphire, Alexandrite, Spinel, Yttrium Orthoaluminate, Potassium Gadolinium Tungstate, Yttrium Orthovandate, or Lanthahum Scandium Borate). Laser element 110 is positioned proximal to pump source 112 and may be arranged in parallel relation therewith, although other geometries and configurations may be employed.
Pump source 112 may be any device or apparatus operable to excite laser element assembly 110. Non-limiting examples of devices which may be used as pump source 112, include: arc lamps, flashlamps, and laser diodes.
A Q-switch 114 disposed within laser unit 102 may be operated in a repetitive mode to cause a train of micropulses to be generated by laser unit 102. Typically the micropulses are less than 1 microsecond in duration separated by about 40 microseconds, creating a quasi-continuous wave train. Q-switch 114 is preferably of the acousto-optic type, but may alternatively comprise a mechanical device such as a rotating prism or aperture, an electro-optical device, or a saturable absorber.
Laser unit 102 is provided with a control system 116 for controlling and operating laser unit 102. Control system 116 will typically include a control processor which receives input from user controls (including but not limited to a beam on/off control, a beam power control, and a pulse duration control) and processes the input to accordingly generate output signals for adjusting characteristics of the output beam to match the user inputted values or conditions. With respect to pulse duration adjustment, control system 116 applies an output signal to a power supply (not shown) driving pump source 112 which modulates the energy supplied thereto, in turn controlling the pulse duration of the output beam. Laser unit 102 further includes an output port 118 couplable to a proximal end 119 of optical fiber 106. Output port 118 directs the light generated by laser unit 102 into optical fiber 106 for delivery to tissue 104.
Although FIG. 1 shows an internal frequency doubled laser, it is only by way of example. The infrared light can be internally or externally frequency doubled using non-linear crystals such as KTP, Lithium Triborate (LBO), or Beta Barium Borate (BBO) to produce 532 nm light. The frequency doubled, shorter wavelength light is better absorbed by the hemoglobin and char tissue, and promotes more efficient tissue ablation.
Referring now to FIGS. 2 and 3, optical fiber 200 of the present invention generally comprises an internal fiber 202 defining a fiber tip 204 at a treatment end 206 of the optical fiber 200. Internal fiber 202 is manufactured from a silicon material, typical of optical fibers. Internal fiber 202 is protected from damage prior to use and during introduction to the treatment location with a protective jacket assembly 206. Projective jacket assembly 206 generally comprises a body tube assembly 208 and a tip cap assembly 210. Body tube assembly 208 generally protects a majority portion of the internal fiber 202, extending from proximal end 119 to the tip cap assembly 210. Body tube assembly 208 generally comprise an internal fiber jacket 212 and an external body tube 214 with a body tube channel 216 defined therebetween. Similar to internal fiber 202, internal fiber jacket 212 and external body tube 214 are constructed of a suitable silicon material.
As illustrated in FIG. 3, tip cap assembly 128 generally comprises an inner cap member 218 and an outer cap member 220 defining a cap irrigation channel 222 therebetween. Together, cap irrigation channel 222 and body tube channel 216 cooperatively define an internal irrigation channel 224. Outer cap member 220 includes a side port 226 positioned within an exterior surface 228. Side port 226 generally defines a radiused edge 230 such that laser energy can be directed from the fiber tip 204 to the treatment location.
In operation, optical fiber 200 and more specifically fiber tip 204 can be introduced to the treatment location utilizing a conventional cystoscope 240 as shown in FIG. 4. Generally, the cystoscope 240 is advanced through the urethra and proximate the treatment area. Once the cystoscope 240 is positioned at the treatment area, an irrigant such as water or saline can be injected through the cystoscope 240. When performing a medical laser procedure with the laser system 100, optical fiber 200 is advanced through the cystoscope 240 such that side port 226 is positioned proximate the desired treatment location.
With the side port 226 oriented toward the treatment location, saline is simultaneously directed through the internal irrigation channel 224 and in an external irrigation channel 242 defined between the cystoscope 240 and the protective jacket assembly 206. With an external cooling stream 244 flowing across exterior surface 228 and between the inner cap member 218 and an internal cooling stream 246 flowing between the outer cap member 220, control system 116 directs laser energy through the optical fiber 200 such that a treatment beam exits the fiber tip 204 and out the side port 226. As the treatment beam contacts the treatment location, heat is generated at a tissue surface as the laser energy ablates the targeted tissue. The dual simultaneous cooling of the external cooling stream 244 and the internal cooling stream 246 remove heat energy from the fiber tip 204. As fiber tip 204 is prevented from overheating, ablated tissue is kept from adhering within or around the side port 226 or to the exterior surface 228. In addition, the outer cap member 220 provides a gap between the fiber tip 204 and the treatment location such that tissue does not attach to the fiber tip 204 due to localized heating at the fiber tip 204. With heat energy removed at the tip cap assembly 210, overheating is avoided such that devitrification and cratering of optical fiber 200 does not occur.
FIG. 5 provides a comparison between the standard 2090 fiber that is typically used with a GreenLight HPS laser treatment device for treatment of benign prostate hyperplasia (BPH) and the fiber with active cooling cap of the present invention. As shown the percentage of transmission of light stays steady in the fiber with the active cooling cap while the 2090 fiber experiences intermittent decreases in transmission of light as energy is increased. As indicated by the graph, the active cooling cap fiber of the present invention provides reduced laser energy absorption by preventing the tissue contact at the laser firing point and the areas adjacent to the firing point; the tissue is in contact with the outer cap rather than the inner cap through which the laser light is being delivered. Further, the irrigation fluid from the about the inner cap pushes the tissue debris out of the firing point of the inner cap and, hence, further prevents tissue debris from depositing and burning at the firing point. Moreover, the active cooling cap of the present invention can provide cooling from inside of the cap even when the irrigation fluid from the cystoscope is totally block by tissue.
Although specific examples have been illustrated and described herein, it will be appreciated by those of ordinary skill in the art that any arrangement calculated to achieve the same purpose could be substituted for the specific examples shown. This application is intended to cove adaptations or variations of the present subject matter. Therefore, it is intended that the invention be defined by the attached claims and their legal equivalents.

Claims

We claim:

1. An optical fiber for medical procedures comprising:

an internal fiber terminating at a fiber tip, the internal fiber being surrounded by a body tube assembly at a proximal portion of the internal fiber and by a tip cap assembly at the fiber tip, the tip cap assembly and body tube defining an internal irrigation channel for cooling the fiber tip during a medical laser procedure.

2. The optical fiber of claim 1, wherein the tip cap assembly comprises an inner cap member and an outer cap member, a cap irrigation channel being defined between the inner cap member and the outer cap member.

3. The optical fiber of claim 2, wherein the body tube assembly comprises an internal fiber jacket and an external body tube, a body tube channel being defined between the internal body tube and the external body tube, and wherein the cap irrigation channel and the body tube channel cooperatively define the internal irrigation channel.

4. The optical fiber of claim 2, wherein the outer cap member includes an exterior surface having a side-firing port for directing laser energy from the fiber tip to a treatment location.

5. The optical fiber of claim 4, wherein the outer cap member provides a physical barrier preventing contact between the fiber tip and the treatment location during a treatment procedure.

6. The optical fiber of claim 1, wherein the body tube assembly and tip cap assembly are adapted for introduction through a cystoscope, whereupon an internal saline flow can be directed through the internal irrigation channel and an external saline flow can be directed between the cystoscope and the body tube assembly and tip cap assembly to simultaneously cool the fiber tip.

7. A method for preventing overheating a medical optical fiber during a medical treatment procedure comprising:

providing an optical fiber having an internal fiber jacket surrounding by a protective jacket assembly, wherein an internal irrigation channel is defined between the internal fiber jacket and the protective jacket assembly;

directing an internal saline flow stream through the internal irrigation channel; and

removing heat energy generated at a fiber tip during treatment with the internal saline flow stream.

8. The method of claim 7, further comprising:

accessing an internal treatment site with a cystoscope; and

advancing the optical fiber through the cystoscope such that the fiber tip is proximate the internal treatment site.

9. The method of claim 8, further comprising:

directing an external saline flow stream through a gap defined between the cystoscope and the protective jacket assembly.

10. The method of claim 7, wherein the protective jacket assembly comprise a tip cap assembly proximate the fiber tip, the tip cap assembly including an inner cap member and an outer cap member, wherein the internal irrigation channel is defined between the inner cap member and the outer cap member.

11. The method of claim 10, further comprising:

directing laser energy from the fiber tip through a side-firing port in the outer cap member.

12. The method of claim 11, further comprising:

preventing adhesion of ablated tissue to the fiber tip by maintaining a physical gap between the fiber tip and a treatment site.

13. A medical laser system comprising:

a laser unit for generating laser treatment energy; and

an optical fiber attached to the laser unit for directing the laser treatment energy to a treatment location, the optical fiber including an internal fiber jacket surrounding by a protective jacket assembly such that an internal irrigation channel is defined between the internal fiber jacket and the protective jacket assembly such that an internal saline flow can be directed through the internal irrigation channel to cool a fiber tip on the optical fiber.

14. The medical laser system of claim 13, further comprising:

a cystoscope for accessing a treatment site within the patients body, the optical fiber adapted for insertion through the cystoscope such that an external saline flow can be directed between the cystoscope and the protective jacket assembly.

15. The medical laser system of claim 13, wherein the external fiber jacket comprises a body tube assembly at a proximal portion of the internal fiber jacket and a tip cap assembly at the fiber tip.

16. The medical laser system of claim 15, wherein the tip cap assembly comprises an outer cap member and an inner cap member, the outer cap member including an exterior surface having a side-firing port for directing laser energy from the fiber tip to the treatment location.

17. The medical laser system of claim 16, wherein the outer cap member provides a physical barrier preventing contact between the fiber tip and the treatment location during a treatment procedure.