A precise medical laser device

Abstract

The present invention provides a precise medical laser device, comprising a medical laser source, an optical sensor, a beam analyzer and an ablation mode controller. By adjusting the human tissue database embedded in the ablation mode controller, the ablation mode controller is used to control the output parameters of the medical laser light source, such as the wavelength, repetition frequency, pulse width and action time of the output laser, thereby achieving rough cutting, fine cutting, carbonization hemostasis / non-carbonization of the diseased tissue, and achieving a variety of tissue ablation effects.

Description

Technical Field

[0001] The present invention relates to the field of laser medical technology, and in particular to a precise medical laser device. Background Art

[0002] Laser irradiation of biological tissues will produce thermal, mechanical, photochemical and other effects, which can be used for the diagnosis and treatment of various diseases. Among them, infrared band lasers are mainly used for ablation of diseased tissues, and their ultimate goal is to effectively remove the diseased tissues while minimizing collateral damage to surrounding tissues. 980 nm lasers are often used for ablation of large organ tumors such as lung tumors and liver tumors. They have the characteristics of fast ablation speed and large collateral damage, but they are not suitable for high-precision clinical surgery. Existing studies have shown that the new mid-infrared laser overlaps with the protein amide-II absorption band. Compared with other wavelengths, this wavelength has minimal collateral damage and higher ablation efficiency when used for ablation of brain nerve tissues and eyes, and is suitable for fine resection of diseased tissues. However, existing technologies are difficult to achieve high-power output in this band. Moreover, it is difficult for common medical lasers to achieve multi-functional and multi-mode laser output, and it is impossible to meet the application requirements of a medical laser for different medical scenarios. Therefore, it is urgent to develop a medical laser source that can be used to achieve rough cutting, fine cutting, carbonization hemostasis / non-carbonization of diseased tissues, and at the same time include high-power laser output in the 1 μm~10 μm band. Summary of the invention

[0003] 1. Purpose of the invention

[0004] The purpose of the present invention is to provide a precise medical laser device that can realize multiple mode outputs, achieve beneficial effects such as fine cutting, rough cutting, carbonization hemostasis, and non-carbonization, thereby meeting various medical application scenarios; at the same time, the laser device can adjust the optical parametric oscillator to accurately operate under degenerate point conditions, and realize high-power, narrow linewidth, and high-efficiency parametric laser output.

[0005] (II) Technical solution

[0006] To solve the above problems, the present invention provides a precise medical laser device, including a medical laser source, an optical sensor, a beam analyzer, an ablation mode controller and an optical path shaping module:

[0007] Medical laser sources include ablation laser sources and indicator light sources. The ablation laser sources include 1 μm~10 μm laser sources and 980 nm laser sources. The 1 μm~10 μm laser sources are used for fine cutting, and the 980 nm laser sources are used for rough cutting:

[0008] The optical sensor is placed in front of the light outlet of the medical laser source and is used to measure the light beam information emitted by the medical laser source;

[0009] The ablation mode controller is used to control the output mode of the laser source. The output modes include fine cutting, rough cutting, carbonization hemostasis, and no carbonization. The ablation mode controller is embedded with a human tissue database.

[0010] The beam analyzer is connected to the medical laser source, the ablation mode controller, and the optical sensor to receive and analyze the beam error between the beam information measured by the optical sensor and the beam information set by the ablation mode controller. , and according to the beam error Adjust the beam information of the ablation laser light source until the beam error The first precondition is met;

[0011] The 1 μm~10 μm laser source includes at least one laser pump source, at least one nonlinear optical crystal, an optical device, and a degenerate phase matching precision control module; the laser pump source is used to emit a first pump light, and the repetition frequency of the first pump light is adjustable; the nonlinear optical crystal is used to generate a first parametric light under the pumping of the first pump light and the second parametric light The optical device comprises an optical parametric oscillator cavity mirror and an etalon, wherein the optical parametric oscillator cavity mirror is placed in the direction of action between the laser pump source and the nonlinear optical crystal, and is located on both sides of the nonlinear optical crystal, for parametric light resonance; the etalon is placed in the direction of action between the laser pump source and the nonlinear optical crystal, and is located between the input cavity mirror and the output cavity mirror, for parametric light mode selection, so as to precisely control the wavelength and achieve line width narrowing of the output parametric light; the degenerate phase matching precise control module comprises a wavelength detector, an analysis controller, and a phase matching controller; the wavelength detector is placed on the side of the optical parametric oscillator, and is used to monitor the first parametric light and the second parametric light , and transmitted to the analysis controller; the analysis controller is used to analyze the wavelength difference of the two parameter lights , and the wavelength difference The phase matching controller transmits the Adjust the phase matching parameters of the nonlinear optical crystal so that the wavelength difference of the generated parametric light is Less than the preset value, the degenerate point wavelength output is achieved.

[0012] Optionally, the phase matching controller includes a pointing positioner, and the pointing positioner includes a pointing positioning adjustment mirror and a positioner.

[0013] The pointing positioning adjustment mirror is placed in the output direction of the first pump light, and the pointing positioning adjustment mirror can move or rotate in three dimensions, front and back, pitch, and swing, and is used to return and adjust the transmission direction of the first pump light; the positioner is placed in the transmission direction of the first pump light, and is used to sense the transmission direction of the first pump light, and adjust the position and / or angle of the pointing positioning adjustment mirror according to the transmission direction of the first pump light and the direction of the optical axis, so that the transmission direction of the first pump light makes its included angle with the direction of the optical axis. The second precondition is met;

[0014] Optionally, the phase matching controller includes a first phase matching controller and a second phase matching controller;

[0015] The first phase matching controller is used to perform a first adjustment on the phase matching parameters of the nonlinear optical crystal, and the second phase matching controller is used to perform a second adjustment on the phase matching parameters of the nonlinear optical crystal so that the wavelength difference of the generated parametric light is Less than the preset value.

[0016] Optionally, the second preset condition is: .

[0017] Optionally, the first phase matching controller performs a first adjustment on the phase matching parameter of the nonlinear optical crystal until , the second phase matching controller adjusts the nonlinear optical crystal for the second time until .

[0018] Optionally, the beam information includes power, wavelength, repetition frequency, pulse width, action time and spot size.

[0019] Optionally, the beam error Including power error , wavelength error , repetition frequency difference , pulse width difference , Action time difference and spot size difference .

[0020] Optionally, the first preset condition is: , , , , , .

[0021] Optionally, the 1 μm~10 μm laser source further includes a parametric optical power amplification module;

[0022] The parametric optical power amplifier module comprises an end-face pump module, a pump source gain medium, a first resonant cavity, a second resonant cavity, an optical element and a nonlinear frequency conversion crystal, wherein the end-face pump module is arranged at the end face of the pump source gain medium for emitting a second pump light; the pump source gain medium is used to absorb the energy of the second pump light and then amplify the first pump light output from the output mirror of the optical parametric oscillator; the first resonant cavity comprises two first cavity mirrors arranged at a small angle on both sides of the pump source gain medium, which are used for the resonance of the first pump laser to realize the amplification of the first pump light, and the amplified first pump light is folded back to the second resonant cavity and enters the second resonant cavity together with the parametric light output from the output mirror of the optical parametric oscillator; the second resonant cavity comprises two second cavity mirrors arranged on both sides of the nonlinear frequency conversion crystal for amplifying and folding the first pump light and the parametric light entering, so that the first pump light returns to the first resonant cavity and is folded back for output; the optical element is used for beam shaping and optical path folding, so that the folded-back output first pump light and the parametric light output from the second resonant cavity are combined for output.

[0023] Optionally, after the etalon mode is selected, the line width of the output parametric light is less than 1 nm.

[0024] Optionally, the indicator light source is a visible light source, including a light source with a wavelength of 400-780 nm.

[0025] Optionally, the parametric optical power amplifier module may include multiple nonlinear frequency conversion crystals to perform multiple optical parametric amplifications.

[0026] (III) Beneficial effects

[0027] 1. In the present invention, by setting an ablation mode controller, the power, wavelength, repetition frequency, pulse width, action time and spot size of the output laser can be controlled, so as to achieve the beneficial effects of fine cutting, rough cutting, carbonization hemostasis and non-carbonization;

[0028] 2. In the present invention, by adding a phase matching precision control module and an intracavity standard tool, the phase matching parameters are changed by temperature modulation, angle modulation and stress modulation, so as to achieve accurate degenerate point wavelength output and obtain high-power, high-conversion-efficiency narrow-linewidth parametric light output;

[0029] 3. The present invention includes a power amplification module, which can effectively increase the output power of 2 μm~10 μm laser and obtain higher power 2 μm~10 μm laser output. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, a brief introduction will be given below to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work, which should be within the protection scope of the patent of the present invention.

[0031] Figure 1 It is a structural schematic diagram of a precision medical laser device provided by the present invention;

[0032] Figure 2 It is a structural schematic diagram of a laser output device for accurately adjusting the wavelength of a degenerate point provided by the present invention;

[0033] Figure 3 It is a structural schematic diagram of a parametric optical power amplifier module provided by the present invention;

[0034] Figure 4 This is a flow chart of the use of a precision medical laser device provided by the present invention;

[0035] Figure 5 This is a flow chart of the use of a laser device for accurately adjusting the wavelength of a degenerate point provided by the present invention;

[0036] Figure 6 This is a diagram showing the effect of accurately adjusting the degenerate point wavelength output provided by the present invention;

[0037] Reference numerals:

[0038] 1-medical laser source, 2-optical sensor, 3-beam analyzer, 4-ablation mode controller, 5-optical path shaping module;

[0039] 11-980nm laser, 12-6450nm laser;

[0040] 121-laser pump source, 122-nonlinear optical crystal, 123-optical device, 124-degenerate phase matching precise control module, 125-power amplification module;

[0041] 123-1-shaping lens, 123-2-etalon, 123-3-input mirror, 123-4-output mirror;

[0042] 124-1-pointing positioning adjustment mirror, 124-2-positioner, 124-3-wavelength detector, 124-4 analysis controller, 124-5-first phase matching controller, 124-6-second phase matching controller;

[0043] 125-1 end pump module, 125-2 pump source gain medium, 125-3 first cavity mirror, including a first input cavity mirror and a first output cavity mirror, 125-4 second cavity mirror, including a second input cavity mirror and a second output cavity mirror, 125-5 optical element, 125-6 nonlinear frequency conversion crystal. DETAILED DESCRIPTION

[0044] In order to make the purpose, technical scheme and advantages of the present invention clearer, the present invention is further described in detail below in conjunction with specific embodiments and with reference to the accompanying drawings. It should be understood that these descriptions are only exemplary and are not intended to limit the scope of the present invention. In addition, in the following description, the description of well-known structures and technologies is omitted to avoid unnecessary confusion of the concept of the present invention.

[0045] The following is combined with Figures 1 to 6 The present invention is described in detail with reference to the accompanying drawings and examples.

[0046] See also Figures 1 to 3 As shown, a precision medical laser device of the present application includes a medical laser source 1, an optical sensor 2, a beam analyzer 3, an ablation mode controller 4 and an optical path shaping module 5.

[0047] The medical laser source 1 includes an ablation laser light source and an indicator light source 13. The ablation laser light source includes a 1 μm~10 μm laser source 11 and a 980 nm laser source 12. The 1 μm~10 μm laser source 11 is used for fine cutting of biological tissues; the 980 nm laser source 12 is used for rough cutting of biological tissues.

[0048] The optical sensor 2 is placed in front of the light outlet of the medical laser source 1 and is used to measure the light beam information emitted by the medical laser source 1. The light beam information includes power, wavelength, repetition frequency, pulse width, action time and spot size. The optical sensor 2 can be a combination of multiple sensors.

[0049] The beam analyzer 3 is connected to the medical laser source 1, the ablation mode controller 4, and the optical sensor 2 for receiving and analyzing the beam error between the beam information measured by the optical sensor 2 and the beam information set by the ablation mode controller 4. , and according to the beam error Adjust the beam information of the ablation laser light source until the beam error The first preset condition is satisfied. In some specific embodiments, the first preset condition is: power error , wavelength error , repetition frequency difference , pulse width difference , action time difference , spot size radius difference Such parameter settings can achieve high-precision ablation laser output and meet the requirements of high-precision medical surgery.

[0050] The ablation mode controller 4 is used to control the output mode of the laser source. The output modes include fine cutting, rough cutting, carbonization hemostasis, and non-carbonization. The ablation mode controller 4 is embedded with a human tissue database. The human tissue database contains the laser beam information required for various ablation modes corresponding to different tissues. The specific selection and setting is made by medical personnel according to actual conditions.

[0051] Furthermore, in some embodiments, the indicator light source 13 is a visible light source, including a light source with a wavelength of 400-780 nm.

[0052] In some embodiments, the optical sensor 2 may be a sensor group including a spectrometer, a photodetector, a spectrometer, an infrared imager, and the like.

[0053] See also Figure 2 The 1 μm~10 μm laser source 11 of the embodiment of the present invention includes a laser pump source 121, a nonlinear optical crystal 122, an optical device 123, and a degenerate phase matching precise control module 124.

[0054] The laser pump source 121 is used to emit pump light, and the repetition frequency of the laser pump source 121 is adjustable within 1 to 10 kHz; the nonlinear optical crystal 122 is used to generate the first parametric light under the pumping of the laser pump source 121 and the second parametric light The optical device 123 includes a shaping lens 123-1, an etalon 123-2, an optical parametric oscillator input mirror 123-3 and an optical parametric oscillator output mirror 123-4, wherein the optical parametric oscillator input mirror 123-3 and the optical parametric oscillator output mirror 123-4 are placed in the direction of action between the laser pump source 121 and the nonlinear optical crystal 122, and are located on both sides of the nonlinear optical crystal 122, for parametric light resonance; the etalon 123-2 is placed in the direction of action between the laser pump source 121 and the nonlinear optical crystal 122, and is located between the optical parametric oscillator input mirror 123-3 and the optical parametric oscillator output mirror 123-4, for parametric light mode selection, so as to precisely control the wavelength and achieve line width narrowing of the output parametric light. The degenerate phase matching precise control module 124 includes a pointing positioning adjustment mirror 124 - 1 , a positioner 124 - 2 , a wavelength detector 124 - 3 , an analysis controller 124 - 4 , a first phase matching controller 124 - 5 and a second phase matching controller 124 - 6 .

[0055] The pointing positioning adjustment mirror 124-1 is placed in the output direction of the first pump light, and is used to return and adjust the transmission direction of the first pump light; the positioner 124-2 is placed in the transmission direction of the first pump light, and is used to sense the transmission direction of the first pump light, and adjust the position and / or angle of the pointing positioning adjustment mirror 124-1 according to the transmission direction of the first pump light and the direction of the optical axis, so that the transmission direction of the first pump light makes its included angle with the direction of the optical axis The wavelength detector 124-3 is placed on the side of the optical parametric oscillator to monitor the first parametric wavelength. and the second parametric light , and transmitted to the analysis controller 124-4; the analysis controller 124-4 is used to analyze the wavelength difference of the two parameter lights , and the wavelength difference The first phase matching controller 124-5 and the second phase matching controller 124-6 transmit the first phase matching controller 124-5 and the second phase matching controller 124-6 according to the wavelength difference. Adjust the phase matching parameters of the nonlinear optical crystal 122 so that the wavelength difference of the generated parametric light is Less than the preset value, the degenerate point wavelength output is achieved, effectively improving the output power and efficiency of the parametric light.

[0056] Furthermore, in some embodiments, the shaping lens 123 - 1 may be a waveguide or a lens group.

[0057] In some embodiments, the etalon 123-2 may be a single or multiple etalon groups, and placed on a turntable, and the angle may be adjusted. Specifically, after the mode of the etalon 123-2 is selected, the line width of the output parametric light is less than 1 nm, thereby achieving line width compression of the parametric light.

[0058] In some embodiments, the OPO input mirror 123 - 3 and the OPO output mirror 123 - 4 may be plane mirrors or curved mirrors coated with different film systems.

[0059] In some embodiments, the pointing positioning adjustment mirror 124 - 1 can move or rotate in three dimensions, forward and backward, in pitch, and in swing, to adjust the propagation direction of the first pump light.

[0060] In some embodiments, the nonlinear optical crystal 122 is placed in a heat sink, which may be made of copper or red copper with good thermal conductivity, which is beneficial to improving the timeliness and effectiveness of temperature control.

[0061] In some embodiments, the first phase matching controller 124-5 and the second phase matching controller 124-6 may be temperature and angle matching controllers and stress control instruments. Specifically, the temperature matching controller may be composed of a crystal heat sink and a temperature regulator, and the temperature regulator is a temperature controller or a water cooler; the angle matching controller may be composed of a crystal heat sink and a turntable, and the heat sink is installed on the turntable. Rotating the turntable drives the rotation of the crystal angle, and the turntable may be a manual or electric turntable; the stress control instrument may be composed of a stress applicator and a stress detector. The stress applicator is placed on both sides of the nonlinear optical crystal, and can change the refractive index of the nonlinear optical crystal by applying stress. The stress detector can monitor the amount of applied stress, thereby obtaining the change in the refractive index of the nonlinear optical crystal.

[0062] In some embodiments, the second preset condition is: , so that the transmission direction of the first pump light coincides with the direction of the optical axis.

[0063] In some embodiments, the first phase matching controller 124-5 performs a first adjustment on the phase matching parameters of the nonlinear optical crystal 122 until , the second phase matching controller 124-6 performs a second adjustment on the nonlinear optical crystal 122 until , according to the sensitivity of different nonlinear optical crystals to temperature, angle and stress, the parameters of the first and second adjustments are determined. For example, ZGP crystal has high angle sensitivity, so the first angle adjustment is performed to meet the requirements. , the second time, the stress can be adjusted to change the refractive index of the ZGP crystal to meet .

[0064] The 1 μm-10 μm laser source 11 of the embodiment of the present invention further includes a parametric optical power amplifier module, see Figure 3 The parametric optical power amplifier module includes an end-face pump module 125-1, a pump source gain medium 125-2, a first cavity mirror 125-3, a second cavity mirror 125-4, an optical element 125-5 and a nonlinear frequency conversion crystal 125-6. The end-face pump module 125-1 is used to emit the second pump light and is placed at the end face of the pump source gain medium 125-2; the pump source gain medium 125-2 is used to absorb the energy of the second pump light and then amplify the first pump light in a superposition manner; the first cavity mirror 125-3 is used for the resonance of the first pump laser and is placed at both sides of the pump source gain medium 125-2 at a small angle; the second cavity mirror 125-4 is used for the resonance of the parametric light and is placed on both sides of the nonlinear frequency conversion crystal 125-6; the optical element 125-5 is used for beam shaping and optical path folding; the nonlinear frequency conversion crystal 125-6 is used for the amplification of the parametric light.

[0065] Furthermore, in some embodiments, the pump source gain medium 125 - 3 may be a rod-shaped crystal or a lath-shaped crystal.

[0066] In some embodiments, the first cavity mirror 125 - 4 is coated with a high reflective film system of the first pump laser.

[0067] In some embodiments, the second cavity mirrors 125 - 5 and 125 - 6 are coated with a partial transmittance film system for the parametric light and the first pump light.

[0068] In some embodiments, there may be one or more nonlinear frequency conversion crystals 125 - 8 .

[0069] The high-precision neurosurgery medical 1 μm~10 μm laser device of the present invention is described below through specific embodiments.

[0070] Example 1

[0071] like Figure 1 As shown, a precise medical laser device provided by an embodiment of the present invention includes a medical laser source 1, an optical sensor 2, a beam analyzer 3, an ablation mode controller 4, and an optical path shaping module 5; wherein the medical laser source 1 includes a 980 nm laser source 11 for rough cutting, a 1 μm~10 μm laser source 12 for fine cutting, and an indicator light source 13 such as a helium-neon indicator laser. According to different ablation mode settings, the 980 nm laser source 11 and the 1 μm~10 μm laser source 12 are selected to work, and at the same time, the laser output of the helium-neon laser completely overlaps with the 980 nm / 2 μm~10 μm laser, which serves as an indicator light to determine the laser action position. The optical path shaping module 5 is placed in front of the medical laser source 1, and is used for outputting laser beam shaping and propagation direction control; the optical sensor 2 is placed in front of the optical path shaping module 5, and is used for receiving and measuring the emission information of the laser source; the beam analyzer 3 is connected to the 980 nm laser source 11 and the 1 μm~10 μm laser source 12, the ablation mode controller 4, and the optical sensor 2, and is used for analyzing the beam error between the beam information received by the optical sensor 2 and the beam information set by the ablation mode controller 4 The output end of the ablation mode controller 4 is connected to a 980 nm laser source 11, a 1 μm~10 μm laser source 12 and a beam analyzer 3, and is used to control the output mode of the laser source. The ablation mode controller 4 is shown to have a human tissue database embedded therein.

[0072] The 1 μm~10 μm laser source 12 used for tissue ablation includes a laser device for accurately adjusting the output of the degenerate point wavelength, such as Figure 2 As shown, it includes a laser pump source 121, a nonlinear crystal 122, optical devices, a degenerate phase precision control module and a power amplification module 125.

[0073] Laser pump source 121 wavelength satisfy ,in, and It is a wavelength signal of two parameter lights, with an adjustable repetition frequency of 10-10 kHz, a power of 100 W and a pulse width of 30 ns.

[0074] The nonlinear crystal 122 is a ZGP crystal or a BGSe crystal with a size of 5×5×30 mm 3 , and works in type I phase matching mode, the main plane is placed parallel to the light propagation direction and perpendicular to the polarization direction of the pump light emitted by the pump source 121, 5×5mm 2 It is the input and output end surface.

[0075] The optical device includes a shaping lens 123-1, an etalon 123-2, an input mirror 123-3 and an output mirror 123-4 of an optical parametric oscillator cavity mirror. The shaping lens 123-1 is placed along the propagation direction of the pump light and can be a lens with different focal lengths coated with a high transmittance of the pump light, and is used to shape the output laser of the pump source 121; the input mirror 123-3 and the output mirror 123-4 constitute a resonant cavity of the optical parametric oscillator, which are placed along the propagation direction of the pump light and are placed on both sides of the crystal, wherein the input mirror 123-3 is coated with a high transmittance film for the pump light and a high reflective film system for the parametric light, and the output mirror 13-4 is coated with a high transmittance film for the pump light and a 50% output transmittance of the parametric light;

[0076] The etalon 123-2 is placed in the direction of action of the laser pump source and the nonlinear optical crystal, and is located between the input cavity mirror and the output cavity mirror. The etalon used in this embodiment has the characteristics of adjustable tilt angle and controllable temperature, and is used for parametric light mode selection to achieve narrow linewidth 2 μm~10 μm laser output.

[0077] The degenerate phase precision control module includes a pointing positioning adjustment mirror 124-1, a positioner 124-2, a wavelength detector 124-3, an analysis controller 124-4, a first phase matching controller 124-5, and a second phase matching controller 124-6. The pointing positioning adjustment mirror 124-1 is placed at 45 degrees and coated with a high reflection film system of the pump light, and is placed along the light output direction of the pump source 121. The first phase matching controller 124-5 is an angle matching controller. The nonlinear crystal 122 is assembled in a heat sink, and the heat sink is installed on an electric turntable. The electric turntable has an accuracy of 0.05 degrees. During the adjustment process, the turntable is adjusted to rotate 0.1 degrees each time, and the nonlinear optical crystal 122 can be rotated along the central symmetry axis of the main plane of the crystal perpendicular to the propagation direction. The second phase matching controller 124-6 is a stress control device placed on both sides of the first phase matching controller 124-5. The refractive index of the nonlinear optical crystal 122 can be changed by applying stress. The stress detector monitors the amount of applied stress, thereby obtaining the change in the refractive index of the nonlinear optical crystal 122. During the stress application process, the control accuracy of the stress applicator is 1 kPa. The analysis controller 124-4 is connected to the pointing positioning adjustment mirror 124-1, the positioner 124-2, the wavelength detector 124-3, the first phase matching controller 124-5 and the second phase matching controller 124-6.

[0078] The parametric optical power amplifier module 125 is as follows Figure 3 As shown, it includes an end pump module 125-2, a pump source gain medium 125-3, a first cavity mirror 125-4, second cavity mirrors 125-5 and 125-6, an optical element 125-7 and a nonlinear frequency conversion crystal 125-8.

[0079] The end pump module 125-2 is a semiconductor or fiber laser, which is used to emit pump light and is placed at the end face of the pump source gain medium. The wavelength is 970 nm and the power is 200 W.

[0080] The pump source gain medium 125-3 is used to absorb the pump light energy and then perform light amplification. It is a slab-shaped Ho, Yb:KYF crystal with a size of 40 mm×10 mm×3 mm.

[0081] The first cavity mirror 125 - 4 is used for the resonance of the pump laser, is placed on both sides of the pump source gain medium 125 - 3 at an angle of 1°, and is coated with a high reflection film for the pump light.

[0082] The second cavity mirrors 125-5 and 125-6 are used for the resonance of parametric light and are placed on both sides of the nonlinear crystal. The optical parametric oscillator input mirror 125-5 is coated with a high-reflection film for parametric light and pump light, and the optical parametric oscillator output mirror 125-6 is coated with a reflective film with a transmittance of 50% for parametric light and a high-reflection film for pump light.

[0083] Optical element 125-7 is used for beam shaping and light path return, and is coated with a high-reflection film for pump light and a high-transmittance film for parametric light.

[0084] Nonlinear frequency conversion crystal 125-8, used for parametric light amplification, is a ZGP crystal or BGSe crystal, with a size of 5×5×30 mm 3 , the main plane is placed parallel to the light propagation direction and perpendicular to the polarization direction of the pump light emitted by the pump source 121, 5×5mm 2 It is the input and output end surface.

[0085] The embodiment of the present invention realizes that the 1 μm~10 μm laser source 12 provides a pulsed laser output with a wavelength of 2 μm~10 μm, an adjustable repetition frequency of 10-10 kHz, and a power of 20 W.

[0086] The embodiment of the present invention provides a precise medical laser device, the working principle of which is as follows: Figure 4 As shown, first, the medical staff sets the ablation mode to precise resection and carbonization hemostasis in the ablation mode controller 4 according to the required ablation scenario, such as brain tumor resection. The ablation mode controller 4 retrieves the embedded human tissue database to set the required laser power, wavelength, repetition frequency, pulse width, action time and spot size and other parameters, and transmits the required parameters to the medical laser source 1 and the beam analyzer 3. The medical laser source 1 selects the laser according to the parameters set by the ablation mode controller 4, outputs the required laser, and transmits the output laser to the optical sensor 2. The optical sensor 2 receives the emitted light beam information and transmits the received information to the beam analyzer 3. The beam analyzer 3 compares the received light beam information with the set parameters of the ablation mode controller 4 to obtain the light beam parameter error, and transmits the light beam parameter error to the medical laser source 1 for output parameter correction. The above process is repeated until the beam error parameter is Meet the preset conditions and obtain the required high-precision neurosurgery medical laser.

[0087] The 2 μm~10 μm laser light source 12 provided in the embodiment of the present invention includes a laser device for accurately adjusting the degenerate point wavelength output, and the degenerate phase precise control module 124 adjusts the phase matching parameters in multiple ways so that the output wavelengths of the two parameter lights meet the preset wavelength difference. , to achieve precise degenerate point output, and by inserting the standard tool 122 into the cavity, the selection of the output parametric light mode is realized, and finally high-power, high-efficiency, narrow-linewidth 2 μm~10 μm laser output is achieved. Its working principle is as follows Figure 5As shown, it includes a wavelength detection and analysis step, a phase matching adjustment step, and multiple phase matching parameter optimization steps. In the wavelength detection and analysis step, the pointing positioning adjustment mirror 124-1 is used to return the laser emitted by the pump source 121, so that the pump laser propagates to the positioner 124-2 along a direction parallel to the transverse optical axis of the nonlinear crystal 122. The positioner 124-2 receives the pump laser signal and transmits the signal to the analysis controller 124-4 for analysis. The analysis controller 124-4 sends an adjustment signal to the pointing positioning adjustment mirror 124-1. The pointing positioning adjustment mirror 124-1 adjusts the front and back, pitch, and swing directions according to the received signal, so that the pump laser propagation direction and the angle between the z-axis and the pump laser are equal. , to achieve preliminary phase matching adjustment; the wavelength detector 124-3 receives the parametric light wavelength signal and , and transmits the wavelength signal to the analysis controller 124-4 for wavelength difference Analysis, the analysis controller 124-4 converts the wavelength difference signal The signals are transmitted to the first phase matching controller 124-5 and the second phase matching controller 124-6, respectively, to adjust the angle and stress of the nonlinear crystal 122, and the above signals are repeated many times until the wavelength difference , and finally achieve the degenerate point wavelength output. For the specific wavelength adjustment process, please refer to Figure 6 shown.

[0088] Finally, the embodiment of the present invention realizes 2 μm~10 μm laser output with high precision, narrow linewidth and high power operation, which can be used for high-precision neurosurgery in the brain, spine, eyes and other parts to achieve fine resection of biological tissues.

[0089] Example 2

[0090] This embodiment proposes a precise medical laser device for rough cutting of large tumors, such as Figure 1 As shown, the difference between it and Example 1 is:

[0091] The 980 nm laser source 11 can provide a continuous laser output with a wavelength of 980 nm and a power of 100 W, or provide a pulsed laser output with a wavelength of 980 nm, a repetition frequency adjustable from 10 to 10 kHz, and a power of 80 W.

[0092] Medical personnel set the ablation mode to rapid resection and carbonization hemostasis in the ablation mode controller 4 according to the required ablation scenario, such as large tumor resection in the liver. The ablation mode controller 4 retrieves the embedded human tissue database to set the required laser power, wavelength, repetition frequency, pulse width, action time and spot size and other parameters, and transmits the required parameters to the medical laser source 1 and the beam analyzer 3. The medical laser source 1 selects the laser according to the parameters set by the ablation mode controller 4, outputs the required laser, and transmits the output laser to the optical sensor 2. The optical sensor 2 receives the emitted light beam information and transmits the received information to the beam analyzer 3. The beam analyzer 3 compares the received light beam information with the set parameters of the ablation mode controller 4 to obtain the light beam parameter error, and transmits the light beam parameter error to the medical laser source 1 for output parameter correction. The above process is repeated until the beam error parameter is The preset conditions are met to obtain the required medical laser output.

[0093] Finally, the embodiment of the present invention realizes high-precision, high-power operation of 980 nm laser output, which is used for the removal of large tumors in the liver, lungs and other parts, and realizes rapid, large-volume ablation of biological tissues.

[0094] It should be understood that the above specific embodiments of the present invention are only used to illustrate or explain the principles of the present invention, and do not constitute a limitation of the present invention. Therefore, any modifications, equivalent substitutions, improvements, etc. made without departing from the spirit and scope of the present invention should be included in the protection scope of the present invention. In addition, the appended claims of the present invention are intended to cover all changes and modifications that fall within the scope and boundaries of the appended claims, or the equivalent forms of such scope and boundaries.

Claims

1. A precision medical laser device, characterized in that: Contains medical laser source, optical sensor, beam profiler, ablation mode controller, optical path shaping module and human tissue database: The medical laser source comprises an ablation laser light source and an indicator light source, wherein the ablation laser light source comprises a 1 μm-10 μm laser source and a 980 nm laser source, wherein the 1 μm-10 μm laser source is used for fine tissue cutting, and the 980 nm laser source is used for rough tissue cutting: The optical sensor is placed in front of the light outlet of the medical laser source and is used to measure the light beam information emitted by the medical laser source; The ablation mode controller is used to control the output mode of the laser source, and the output modes include fine cutting, rough cutting, carbonization hemostasis, and non-carbonization. The ablation mode controller is embedded with a human tissue database; the human tissue database records the output mode and beam error of the laser source, and can automatically select the working mode according to the lesion; The beam analyzer is communicatively connected with the medical laser source, the ablation mode controller, and the optical sensor, and is used to receive and analyze the beam error ΔE between the beam information measured by the optical sensor and the beam information set by the ablation mode controller, and adjust the beam information of the ablation laser light source according to the beam error ΔE until the beam error ΔE meets the first preset condition; The 1 μm~10 μm laser source includes at least one laser pump source, at least one nonlinear optical crystal, an optical device, and a degenerate phase matching precision control module; the laser pump source is used to emit a first pump light, and the repetition frequency of the first pump light is adjustable; the nonlinear optical crystal is used to generate a first parametric light λ under the pumping of the first pump light s and the second parametric light λ i The optical device comprises an optical parametric oscillator and an etalon, wherein the optical parametric oscillator comprises an input mirror and an output mirror, which are placed in the direction of action between the laser pump source and the nonlinear optical crystal and on both sides of the nonlinear optical crystal for parametric light resonance; the etalon is placed in the direction of action between the laser pump source and the nonlinear optical crystal and between the input mirror and the output mirror for parametric light mode selection to precisely control the wavelength and achieve line width narrowing of the output parametric light; the degenerate phase matching precise control module comprises a wavelength detector, an analysis controller and a phase matching controller; the wavelength detector is placed on the side of the optical parametric oscillator for monitoring the first parametric light λ s and the second parametric light λ i , and transmit it to the analysis controller; the analysis controller is used to analyze the wavelength difference Δλ between the two parametric lights, and transmit the wavelength difference Δλ to the phase matching controller; the phase matching controller adjusts the phase matching parameters of the nonlinear optical crystal according to the wavelength difference Δλ, so that the wavelength difference Δλ of the generated parametric light is less than a preset value, thereby realizing the degenerate point wavelength output.

2. The precision medical laser device according to claim 1, characterized in that: The phase matching controller includes a pointing positioner, which includes a pointing positioning adjustment mirror and a positioner; the pointing positioning adjustment mirror is placed in the output direction of the first pump light, and the pointing positioning adjustment mirror can move or rotate in three dimensions, front and back, pitch, and swing, and is used to return and adjust the transmission direction of the first pump light; the positioner is placed in the transmission direction of the first pump light, and is used to sense the transmission direction of the first pump light, and adjust the position and / or angle of the pointing positioning adjustment mirror according to the transmission direction of the first pump light and the optical axis direction, so that the angle Δα between the transmission direction of the first pump light and the optical axis direction meets the second preset condition.

3. The precision medical laser device according to claim 2, characterized in that: The phase matching controller also includes a first phase matching controller and a second phase matching controller; the first phase matching controller is used to perform a first adjustment on the phase matching parameters of the nonlinear optical crystal, and the second phase matching controller is used to perform a second adjustment on the phase matching parameters of the nonlinear optical crystal, so that the wavelength difference Δλ of the generated parametric light is less than a preset value.

4. A precision medical laser device according to claim 3, characterized in that: The first phase matching controller and the second phase matching controller include a stress controller, and the stress controller is used to apply stress to the nonlinear optical crystal so that the refractive index of the nonlinear optical crystal changes with the stress.

5. The precision medical laser device according to claim 3, characterized in that: The second preset condition is: Δα<1mrad; The first phase matching controller performs a first adjustment on the phase matching parameter of the nonlinear optical crystal until Δλ<5nm, and the second phase matching controller performs a second adjustment on the nonlinear optical crystal until Δλ<1nm.

6. The precision medical laser device according to claim 1, characterized in that: The beam information includes power, wavelength, repetition frequency, pulse width, action time and spot size.

7. The precision medical laser device according to claim 5, characterized in that: The beam error Including power error ΔP, wavelength error ΔL, repetition frequency difference ΔT, pulse width difference Δτ, action time difference Δt and spot size difference Δω; the first preset condition is: ΔP<0.01W, ΔL<5nm, T=0, Δτ<1ns, Δt<0.5s, Δω<0.01mm.

8. The precision medical laser device according to any one of claims 1 to 7, characterized in that: The 1 μm~10 μm laser source also includes a parametric optical power amplifier module, which includes an end-face pump module, a pump source gain medium, a first resonant cavity, a second resonant cavity, an optical element and a nonlinear frequency conversion crystal, wherein the end-face pump module is placed at the end face of the pump source gain medium to emit a second pump light; the pump source gain medium is used to absorb the energy of the second pump light and then perform overlapping amplification on the first pump light output from the optical parametric oscillator output mirror; the first resonant cavity includes two first cavity mirrors placed at a small angle on both sides of the pump source gain medium, which are used to The first pump light is amplified by the resonance of the first pump laser, and the amplified first pump light is folded back to the second resonant cavity, and enters the second resonant cavity together with the parametric light output from the output mirror of the optical parametric oscillator; the second resonant cavity includes two second cavity mirrors arranged on both sides of the nonlinear frequency conversion crystal to amplify and fold back the first pump light and parametric light entering, so that the first pump light returns to the first resonant cavity and is folded back for output; the optical element is used for beam shaping and optical path folding, so that the folded output first pump light and the parametric light output from the second resonant cavity are combined for output.

9. The precision medical laser device according to claim 1, characterized in that: After the etalon mode is selected, the line width of the output parametric light is less than 1 nm.

10. The precision medical laser device according to claim 8, characterized in that: The parametric optical power amplifier module includes a plurality of nonlinear frequency conversion crystals and performs multiple optical parametric amplifications.

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