CN109431598B - Double-optical fiber laser treatment device - Google Patents
Double-optical fiber laser treatment device Download PDFInfo
- Publication number
- CN109431598B CN109431598B CN201811243497.4A CN201811243497A CN109431598B CN 109431598 B CN109431598 B CN 109431598B CN 201811243497 A CN201811243497 A CN 201811243497A CN 109431598 B CN109431598 B CN 109431598B
- Authority
- CN
- China
- Prior art keywords
- laser
- fiber
- optical fiber
- photothermal
- photothermal material
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B2018/2005—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser with beam delivery through an interstitially insertable device, e.g. needle
Abstract
The invention provides a double-fiber laser treatment device, which is characterized in that two laser transmission channels are arranged, wherein a photo-thermal material is arranged on the end face of a contact type optical fiber, the high-efficiency photo-thermal conversion of the photo-thermal material is utilized to improve the heat production capacity of a probe and improve the temperature of the tail end of the optical fiber, the optical fiber is directly contacted with a tissue in the operation process and then is matched with laser emitted by the non-contact optical fiber, so that high temperature and laser simultaneously act on the tissue, the operation efficiency is greatly improved, the required laser power is greatly reduced compared with that of the traditional optical fiber non-contact method, and the problem of the.
Description
Technical Field
The invention relates to the field of medical equipment, in particular to a double-fiber laser treatment device.
Background
Lasers have gained considerable attention in the field of surgery because of their very good cutting power, good coagulation and little thermal damage. The high-energy pulse laser generated by the laser is transmitted out through the optical fiber, the optical fiber enters the human body through the endoscope, the energy of the laser is transmitted into the part needing laser treatment, and effective and safe treatment is carried out on a patient by utilizing the characteristics of high energy, collimation, short action time, small heat affected area and the like of the laser. The interaction of laser light on biological tissue is the physical basis of medical applications, and the thermal effect of laser light is one of the most widely used and earliest recognized effects of laser tissue in medicine. The laser light is incident on the tissue of the living body, and the absorbed light energy is converted into heat in the light penetration depth range. When the heating rate (the heat energy comes from laser irradiation, and is related to two factors of laser intensity and tissue absorption coefficient) is far higher than the rate of heat required for vaporizing the tissue, the tissue is vaporized and ablated quickly.
The thulium-doped fiber laser can output laser with the wavelength of 1.65-2.1 um, is the widest of all rare earth ions, and has the advantages of simple structure, high efficiency, good heat dissipation characteristic, narrow line width, high quality of output laser beams and the like compared with a solid laser, so that the thulium fiber laser with high peak power pulse output is widely researched in recent years. However, the thulium-doped fiber laser with the wavelength of about 2 μm needs larger pulse energy for cutting and gasifying the tissues, and the laser power is mainly provided by the thulium-doped fiber core. However, with the significant enhancement of the optical power density in the thulium-doped gain fiber, a severe thermal effect occurs, which causes phenomena such as thermal birefringence, phase distortion, thermal focusing, thermal lens, etc., which seriously affects the output power and beam quality of the laser, and becomes a fatal factor for limiting the performance improvement of the laser.
Chinese patent publication No. CN104638506A discloses a 1.9 micron high-power prostate laser therapeutic apparatus, which can perform compensation in different ways for different operating powers, and solve the problems of efficiency reduction and light beam quality deterioration of thulium-doped fiber laser in order to increase power. But this solution still does not solve the problem of thermal effects of the fiber.
CN107412957A discloses a photothermal therapy probe based on photothermal nano material, which comprises a cylindrical shell with one end closed, and photothermal nano material filled in the closed end inside the shell, and kills tumor and other pathological tissue cells by implementing high temperature. However, this solution only uses high temperature to perform the treatment, and it encloses the nano-material in the housing, which is complicated in structure and inefficient in heat generation.
Disclosure of Invention
In order to solve the problems, the invention provides a double-fiber laser treatment device, which is characterized in that two laser transmission channels are arranged, a photothermal material is arranged on the end face of a contact type optical fiber, the heat production capacity of a probe is improved by utilizing the efficient photothermal conversion of the photothermal material, the temperature of the tail end of the optical fiber is improved, the optical fiber is directly contacted with a tissue in the operation process and then is matched with laser emitted by the non-contact optical fiber, so that high temperature and laser act on the tissue simultaneously, the operation efficiency is greatly improved, the required laser power is greatly reduced compared with that of a traditional optical fiber non-contact method, and the problem of the thermal effect of.
The technical scheme of the invention is as follows: the utility model provides a two fiber laser treatment device, the device includes the insert tube, be provided with working channel in the insert tube, be provided with contact laser transmission optic fibre and non-contact laser transmission optic fibre in the working channel, wherein be formed with the optothermal material on the terminal surface of contact laser transmission optic fibre. The photo-thermal material covers the end face of the optical fiber, and the high-efficiency photo-thermal conversion of the photo-thermal material improves the heat generating capacity of the probe and the temperature of the optical fiber.
Preferably, the optical fiber with the photothermal material at the distal end is capable of moving axially within the working channel and can be extended out of the working channel to directly contact tissue during a surgical procedure.
Preferably, both the contact laser transmission fiber and the non-contact laser transmission fiber transmit output laser light from the thulium doped gain fiber.
Preferably, the contact laser transmission fiber and the non-contact laser transmission fiber can transmit laser with different wavelengths, the contact laser fiber with the end surface provided with the photo-thermal material transmits pump light directly from a pump source, and the non-contact laser transmission fiber transmits output laser from the thulium-doped gain fiber.
Preferably, the contact type laser transmission fiber and the non-contact type laser transmission fiber are located in different working channels, and the tail end of the working channel where the non-contact type laser transmission fiber is located is provided with the transparent light exit window, so that the fibers cannot be polluted in the using process and can be reused.
The photo-thermal material can be formed on the surface of the optical fiber by any one of coating, vapor deposition, magnetron sputtering, evaporation and welding. The fusion bonding is performed under a protective atmosphere using an atmosphere composed of He gas, which is effective in preventing oxidation of the material at high temperatures.
The photothermal material may be one or more of a metallic photothermal material, diamond, or a semiconductor material.
Preferably, the photothermal material is a nanomaterial.
The photo-thermal nano material may be one or more of a metal photo-thermal nano material, a nano diamond or a semiconductor nano material.
The metal photo-thermal nano material can be one or more of gold, platinum and palladium nano materials.
The semiconductor nano material can be one or more of copper sulfide, molybdenum sulfide, bismuth sulfide, antimony sulfide, gold sulfide copper selenide, molybdenum selenide, bismuth selenide, antimony selenide or gold selenide.
The density and thickness of the photothermal material are set according to the laser power and clinical temperature requirements. For example, the thickness may be 100 micrometers or less, further, 50 micrometers or less, further, 1 micrometer or less, further, 500 nanometers or less and not less than 1 nanometer.
Further, the apparatus includes a temperature sensor disposed near the fiber tip to monitor the temperature.
Further, the device comprises a cooling and cleaning channel for spraying liquid to the target part to clean and cool the target part.
Compared with the prior art, the invention has the following beneficial effects:
1. the probe intervenes in a focus tissue part through minimally invasive, the temperature of the optical fiber is increased through a high-efficiency photothermal conversion mechanism of photothermal materials on the end face of the contact type optical fiber, the optical fiber contact type and non-contact type laser combined surgical operation is carried out, high temperature and laser simultaneously act on the tissue, so that the operation efficiency is greatly improved, the laser operation has the characteristics of high energy, collimation, short action time and small heat affected zone, meanwhile, the required laser power is greatly reduced compared with that of the traditional optical fiber non-contact type method, and the heat effect problem of the optical fiber is reduced.
2. The optical fiber is directly contacted with the photo-thermal material, the structure is simple, and in addition, the loss of laser energy is greatly reduced.
3. The system complexity is low. Because the power of the product is low, and the temperature of other parts except the pinhead can not rise during working, a water cooling system is not needed, and the complexity of the system is greatly reduced.
Drawings
Fig. 1 is a schematic structural diagram of a laser treatment device.
Fig. 2 is a schematic view of a light source structure of the laser treatment device.
The figure illustrates that 1 is an optical fiber, and 2 is a photo-thermal material.
Detailed Description
In order to make the objects, technical solutions and advantageous technical effects of the present invention clearer, the present invention is further described in detail with reference to the following embodiments. It should be understood that the embodiments described in this specification are only for explaining the present invention and are not to be limited thereto, and the specific parameter settings and the like of the embodiments can be selected according to the circumstances without substantially affecting the results.
Example 1
As shown in fig. 1, the dual-fiber laser treatment device comprises an insertion tube, a working channel is arranged in the insertion tube, two laser transmission fibers 1 and 2 are arranged in the working channel, the fiber 1 is a non-contact fiber, the fiber 2 is a contact fiber, and a photo-thermal material is formed on the end face of the end of the fiber. The photo-thermal material covers the end face of the optical fiber, and the high-efficiency photo-thermal conversion of the photo-thermal material improves the heat generating capacity of the probe and the temperature of the optical fiber.
The photo-thermal material is a metal nano photo-thermal material. The metal photo-thermal nano material is a gold nanosphere.
The metal nano photothermal material is formed on the surface of the optical fiber 2 by fusion. And contacting the tail end of the optical fiber 2 with the gold nanosphere for fusion welding. There are three ways of heating and melting: arc welding; clearing flame and welding; and (4) laser welding. The fusion bonding is performed under a protective atmosphere using an atmosphere composed of He gas, which is effective in preventing oxidation of the material at high temperatures.
The density and thickness of the photothermal material are set according to the laser power and clinical temperature requirements. For example, the thickness may be 100 micrometers or less, further, 50 micrometers or less, further, 1 micrometer or less, further, 500 nanometers or less and not less than 1 nanometer.
The optical fiber 2 with the photothermal material at the end can move axially and can extend out of the working channel to directly contact with the tissue during the operation.
Both laser transmission fibers transmit the output laser light from the thulium-doped gain fiber 6. The output laser of the thulium-doped gain fiber 6 is divided into two beams by the beam splitter 8, and the two beams are transmitted through the optical fibers 1 and 2 respectively.
The two transmission optical fibers are positioned in different working channels, the non-contact optical fiber 1 is provided with a transparent light exit window 9 in the working channel, and the optical fibers cannot be polluted in the using process and can be reused.
Example 2
As shown in fig. 1, the dual-fiber laser treatment device comprises an insertion tube, a working channel is arranged in the insertion tube, two laser transmission fibers 1 and 2 are arranged in the working channel, the fiber 1 is a non-contact fiber, the fiber 2 is a contact fiber, and a photo-thermal material is formed on the end face of the end of the fiber. The photo-thermal material covers the end face of the optical fiber 2, and the high-efficiency photo-thermal conversion of the photo-thermal material improves the heat generating capacity of the probe and the temperature of the optical fiber.
The photo-thermal material is a metal nano photo-thermal material. The metal photo-thermal nano material is a gold nanosphere.
The metal nano photothermal material is formed on the surface of the optical fiber 2 by fusion. And contacting the tail end of the optical fiber 2 with the gold nanosphere for fusion welding. There are three ways of heating and melting: arc welding; clearing flame and welding; and (4) laser welding. The fusion bonding is performed under a protective atmosphere using an atmosphere composed of He gas, which is effective in preventing oxidation of the material at high temperatures.
The density and thickness of the photothermal material are set according to the laser power and clinical temperature requirements. For example, the thickness may be 100 micrometers or less, further, 50 micrometers or less, further, 1 micrometer or less, further, 500 nanometers or less and not less than 1 nanometer.
The contact optical fiber 2 with the end provided with the photo-thermal material can move along the axial direction and can extend out of the working channel to directly contact with tissues in the operation process.
Two laser transmission optic fibre 1 and 2 transmit the laser of different wavelength, and the pumping light becomes two bundles through 8 beam splitting of beam splitter, and one of them directly gets into laser fiber 2, and another beam gets into through chamber mirror 5 and mixes thulium gain optic fibre 6, and the output laser of mixing thulium gain optic fibre 6 transmits through optic fibre 1.
The two transmission optical fibers are positioned in different working channels, the non-contact optical fiber 1 is provided with a transparent light exit window 9 in the working channel, and the optical fibers cannot be polluted in the using process and can be reused.
Although the preferred embodiments of the present patent have been described in detail, the present patent is not limited to the above embodiments, and various changes can be made without departing from the spirit of the present patent within the knowledge of those skilled in the art.
Claims (6)
1. A dual-fiber laser therapy device is characterized in that the device comprises an insertion tube, a working channel is arranged in the insertion tube, two laser transmission fibers are arranged in the working channel, a photothermal material, namely, a fiber with a photothermal material at the tail end is formed on the tail end face of one laser transmission fiber, the fiber with the photothermal material at the tail end can move along the axial direction in the working channel of the insertion tube, the two laser transmission fibers are positioned in different working channels, the fiber without the photothermal material at the end face is provided with a transparent light exit window at the tail end of the working channel, and the photothermal material is formed on the surface of the laser transmission fiber by any one method of coating, vapor deposition, magnetron sputtering, evaporation and welding; two laser transmission optical fiber transmission different wavelength's laser, the end face area photothermal material's laser transmission optical fiber transmission directly comes from the pump light of pumping source, and another laser transmission optical fiber transmission comes from the output laser of doping thulium gain optic fibre, the photothermal material turns into the high temperature with the pump light, the high temperature with the output laser that comes from doping thulium gain optic fibre acts on the tissue simultaneously.
2. The laser treatment apparatus according to claim 1, wherein the welding is performed under a protective atmosphere using an atmosphere consisting of He gas.
3. The laser therapy device according to claim 1, wherein the photothermal material is one or more of a metallic photothermal material, diamond, or a semiconductor material.
4. The laser therapy apparatus according to claim 1, wherein the photothermal material is a nanomaterial.
5. The laser therapy device according to claim 4, wherein the nanomaterial is one or more of a metallic photothermal nanomaterial, nanodiamond, or a semiconductor nanomaterial.
6. The laser therapy apparatus according to claim 1, wherein the apparatus includes a temperature sensor disposed near the fiber tip to monitor temperature.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811243497.4A CN109431598B (en) | 2018-10-24 | 2018-10-24 | Double-optical fiber laser treatment device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811243497.4A CN109431598B (en) | 2018-10-24 | 2018-10-24 | Double-optical fiber laser treatment device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN109431598A CN109431598A (en) | 2019-03-08 |
| CN109431598B true CN109431598B (en) | 2020-06-02 |
Family
ID=65547465
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201811243497.4A Active CN109431598B (en) | 2018-10-24 | 2018-10-24 | Double-optical fiber laser treatment device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109431598B (en) |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1041273A (en) * | 1988-09-23 | 1990-04-18 | 忝觅里雷射系统有限公司 | Heating duct with thermal boundary |
| US5776092A (en) * | 1994-03-23 | 1998-07-07 | Erbe Elektromedizin Gmbh | Multifunctional surgical instrument |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4261167B2 (en) * | 2002-11-29 | 2009-04-30 | Ｈｏｙａ株式会社 | Photothermal actuator and device equipped with photothermal actuator |
-
2018
- 2018-10-24 CN CN201811243497.4A patent/CN109431598B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1041273A (en) * | 1988-09-23 | 1990-04-18 | 忝觅里雷射系统有限公司 | Heating duct with thermal boundary |
| US5776092A (en) * | 1994-03-23 | 1998-07-07 | Erbe Elektromedizin Gmbh | Multifunctional surgical instrument |
Also Published As
| Publication number | Publication date |
|---|---|
| CN109431598A (en) | 2019-03-08 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US6179830B1 (en) | Laser probe | |
| US5180378A (en) | Laser surgery system | |
| Jackson et al. | Diode‐pumped fiber lasers: A new clinical tool? | |
| US6458120B1 (en) | Laser surgical cutting probe and system | |
| US9681917B2 (en) | Fiber laser system for medical applications | |
| JP2012510345A (en) | Laser induced vapor / plasma media medical treatment and apparatus | |
| CN111050682A (en) | Non-ablative photonic devices and related methods | |
| Bonner et al. | Quantification of tissue effects due to a pulsed Er: YAG laser at 2.9 gm with beam delivery in a wet field via zirconium fluoride fibers | |
| CN109381257B (en) | Laser treatment system combining laser and photothermal treatment | |
| CN109567934B (en) | Double-optical-fiber laser treatment system | |
| CN109567933B (en) | Double-optical fiber laser treatment device | |
| CN109431598B (en) | Double-optical fiber laser treatment device | |
| RU2693673C1 (en) | Laser system for selective treatment of acne | |
| CN109116468B (en) | A kind of optical fiber and preparation method thereof of the end for laser therapy with optothermal material | |
| JP3577653B2 (en) | Dental gas laser device | |
| JP7061566B2 (en) | Laser device for selective treatment of acne that reduces the temperature rise of the skin | |
| CN109276818A (en) | A kind of laser fiber shield | |
| CN109452969B (en) | A kind of laser surgey optical fiber of the flexible end with optothermal material | |
| WO2008072033A1 (en) | A surgical apparatus and a method for treating biological hard tissues, particularly for dental surgery, based on a fibre laser | |
| JPH11271564A (en) | Optical connector | |
| CN109567931A (en) | A kind of replaceable laser probe and device for laser therapy of the end with optothermal material | |
| AU3754699A (en) | Apparatus for and method of laser surgery of hard tissues | |
| Beltran Bernal | Laser and wave-guides system for endoscopic/fiberscopic laser surgery | |
| CN107928788B (en) | Semiconductor laser surgery system | |
| WO1990012619A1 (en) | Laser surgery system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |