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WO2024060314A1 - Dispositif de traitement médical et sonde de traitement - Google Patents

Dispositif de traitement médical et sonde de traitement Download PDF

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Publication number
WO2024060314A1
WO2024060314A1 PCT/CN2022/123856 CN2022123856W WO2024060314A1 WO 2024060314 A1 WO2024060314 A1 WO 2024060314A1 CN 2022123856 W CN2022123856 W CN 2022123856W WO 2024060314 A1 WO2024060314 A1 WO 2024060314A1
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WO
WIPO (PCT)
Prior art keywords
probe
litt
laser
lens
target object
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.)
Ceased
Application number
PCT/CN2022/123856
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English (en)
Chinese (zh)
Inventor
崔小飞
符钰棋
纳西尔 古尔扎里 穆罕默德
陈士行
陈默扬
王引言
王鹏
朱磊
李胜中
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shanghai Hroct Litt Medical Technology Co Ltd
Original Assignee
Shanghai Hroct Litt Medical Technology Co Ltd
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Priority claimed from CN202211151254.4A external-priority patent/CN117770947A/zh
Priority claimed from CN202211159480.7A external-priority patent/CN117338407A/zh
Priority claimed from CN202211156542.9A external-priority patent/CN117530770A/zh
Application filed by Shanghai Hroct Litt Medical Technology Co Ltd filed Critical Shanghai Hroct Litt Medical Technology Co Ltd
Priority to US17/980,444 priority Critical patent/US20240001487A1/en
Priority to US17/980,409 priority patent/US20240000507A1/en
Publication of WO2024060314A1 publication Critical patent/WO2024060314A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • 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
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
    • F16H—GEARING
    • F16H27/00—Step-by-step mechanisms without freewheel members, e.g. Geneva drives
    • F16H27/02—Step-by-step mechanisms without freewheel members, e.g. Geneva drives with at least one reciprocating or oscillating transmission member
    • G—PHYSICS
    • G05—CONTROLLING; REGULATING
    • G05D—SYSTEMS FOR CONTROLLING OR REGULATING NON-ELECTRIC VARIABLES
    • G05D23/00—Control of temperature
    • G05D23/19—Control of temperature characterised by the use of electric means
    • G05D23/20—Control of temperature characterised by the use of electric means with sensing elements having variation of electric or magnetic properties with change of temperature

Definitions

  • the present invention relates to the field of medical diagnosis and treatment, and in particular to a medical treatment device and a treatment probe.
  • Laser interstitial thermotherapy is a treatment method that uses the thermal effect of laser to destroy target tissue. It is also the latest minimally invasive surgery for the treatment of brain tumors.
  • the basic principle is to use the stereotactic method in neurosurgery to insert an optical fiber probe with a cooling circulation sleeve into the patient's brain lesion. During treatment, the laser reaches the probe through the optical fiber, thereby heating the lesion tissue around the probe. achieve the purpose of ablation.
  • MRg magnetic resonance-guided
  • the current LITT system has the following problems: (1) Magnetic resonance thermal imaging (MRTI) is used to measure the temperature of the distal and surrounding ablation target lesions of the LITT probe system. Due to the long distance from the target lesion, MRTI temperature measurement is difficult to guarantee. The accuracy of real-time temperature control and detection often requires additional algorithm estimation for non-real-time compensation, which usually has hysteretic subjectivity in algorithm theory, making it difficult to quantify and avoid thermal damage to surrounding healthy tissue; (2) High-power LITT As the core structure of the LITT probe, the diffusion applicator is not uniform enough in manufacturing process, and the physical scattering units are too concentrated.
  • MRTI Magnetic resonance thermal imaging
  • the medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermotherapy (LITT) device including: a LITT probe based on In the magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element is integrated with the LITT probe into an integrated probe, and the temperature measurement element is The element is configured to obtain the temperature of the target object.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermotherapy
  • the temperature measuring element includes a K-type thermocouple.
  • the K-type thermocouple is close to the target object to collect temperature changes of the target object in real time.
  • the temperature measurement element includes a fiber Bragg grating (FBG) sensor.
  • FBG fiber Bragg grating
  • MFD
  • the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity of the FBG and the thermal sensitivity of the FBG, S FSG , by The relationship between the wavelength drift ⁇ S and the temperature change ⁇ T is determined by calibration.
  • the relationship between the Bragg wavelength shift ⁇ S and the temperature change ⁇ T is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor.
  • the reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator.
  • the telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
  • the medical treatment device further includes an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
  • OCT optical coherence tomography
  • the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal.
  • the optical signal has two different central wavelengths.
  • the OCT probe, the LITT probe and the temperature measurement element are integrated into the integrated probe.
  • the medical treatment device further includes: a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable are respectively connected to The translation control mechanism and the rotation control mechanism, which are connected to the LITT probe, control the translation movement of the LITT probe respectively through the translation cable and the rotation cable. and rotational motion.
  • a driving device including: a translation cable and a rotation cable, and a translation control mechanism and a rotation control mechanism, wherein the translation cable and the rotation cable are respectively connected to The translation control mechanism and the rotation control mechanism, which are connected to the LITT probe, control the translation movement of the LITT probe respectively through the translation cable and the rotation cable. and rotational motion.
  • the translation control mechanism includes a worm gear assembly and a timing belt transmission assembly
  • the rotation control mechanism includes a timing belt transmission assembly
  • the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  • the LITT lateral ablation probe includes: a probe body; and a coating covering the end surface of the probe body, wherein the end surface of the probe body and the axis of the probe body form a first angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the coating is a noble metal target coating.
  • the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
  • the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
  • the LITT lateral ablation probe includes: a probe body; and a lens connected to an end surface of the probe body, wherein the end surface of the probe body is perpendicular to the axis of the probe body, so The lens has a first vertex angle, the probe body includes a needle core and a hard cladding located on the outer periphery of the needle core, and the lens is a sapphire lens.
  • the lens is a beveled cylindrical lens, or a beveled hemispherical or hemispherical lens.
  • the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
  • the LITT circumferential ablation probe includes: a probe body, the probe body includes a conical surface, the conical surface is provided with grooves, the grooves are evenly distributed on the conical surface in a pattern, wherein the laser generated by the LITT probe is emitted from the grooves.
  • the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 ⁇ m, and the preset diameter is 100 ⁇ m.
  • the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
  • the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm.
  • the laser is attenuated to 6.6 to 11.2W by the laser power attenuator.
  • the attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit.
  • the power of the two laser beams is equal.
  • the two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
  • the pattern-like grooves evenly distributed on the tapered surface are formed by performing the following operations: fixing both ends of the workpiece to be carved to the slide rail and the fixing device respectively; the laser controller controls the laser emission Laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused to the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the third concave lens A concave lens and a first convex lens are used to expand the diameter of the laser beam to a first diameter, and the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be engraved to form a light spot, the diameter of the light spot is 45 ⁇ m; and movement The drive controller controls the motion driver to drive the movement of the workpiece to be carved.
  • the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe.
  • Polarity intensity wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  • LITT laser interstitial thermal therapy
  • the LITT lateral ablation probe comprises a probe body; and a coating covering the end face of the probe body, wherein the end face of the probe body forms a first angle with the axis of the probe body, the probe body comprises a needle core and a hard cladding located on the outer periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of technology enhanced cladding silica (TECS) material, and the coating is a precious metal target coating.
  • LITT lateral ablation probe comprises a probe body; and a coating covering the end face of the probe body, wherein the end face of the probe body forms a first angle with the axis of the probe body, the probe body comprises a needle core and a hard cladding located on the outer periphery of the needle core, the needle core is made of pure silica material, the hard cladding is made of technology enhanced cladding silica (TECS) material, and the coating is a
  • the plating layer has a double-layer structure, the layer close to the end surface of the probe body is pure silver, and the layer far away from the end surface of the probe body is silicon monoxide.
  • the thickness of the layer close to the end face of the probe body is 100 nm
  • the thickness of the layer far away from the end face of the probe body is 150 nm
  • the plating layer and the axis of the probe body are at a second second angle.
  • the included angle is, and the second included angle is 47°.
  • the LITT lateral ablation probe is obtained by smoothing the end surface of the probe body, and then covering the smoothed end surface with the coating by magnetron sputtering coating.
  • LITT lateral ablation probe for LITT equipment, characterized in that the LITT lateral ablation probe includes: a probe body; and a probe connected to the A lens on the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body includes a needle core and a hard package located on the outer periphery of the needle core layer, the needle core is made of pure silicon dioxide material, the hard cladding is made of TECS material, and the lens is a sapphire lens.
  • LITT lateral ablation probe includes: a probe body; and a probe connected to the A lens on the end face of the probe body, wherein the end face of the probe body is perpendicular to the axis of the probe body, the lens has a first vertex angle, the probe body includes a needle core and a hard package located on the outer periphery of the needle core layer, the needle core is made of pure silicon dioxide material, the hard
  • the lens is a beveled cylindrical lens, or a beveled hemispherical or semi-ellipsoidal lens.
  • the LITT lateral ablation probe is produced by smoothing the end surface of the probe body, welding the probe body and the lens, and performing fire polishing on the welded surface. owned.
  • LITT laser interstitial thermotherapy
  • the LITT probe circumferential ablation includes: a probe body, and the probe body It includes a tapered surface, and grooves are provided on the tapered surface. The grooves are evenly distributed on the tapered surface in a pattern, and the laser light generated by the LITT probe is emitted from the grooves.
  • the diameter of the tapered surface gradually decreases from an initial diameter to a preset diameter, where the initial diameter is 630 ⁇ m, and the preset diameter is 100 ⁇ m.
  • the pattern includes a single thread shape, a cross-thread shape or a diamond grid shape or a combination thereof.
  • the tapered surface is formed by performing the following operations: fixing both ends of the tapered workpiece to be carved on the slide rail and the fixing device respectively; the laser controller controls the laser to emit laser, and the power of the laser is 30W, The wavelength is 10600nm.
  • the laser is attenuated to 6.6 to 11.2W by the laser power attenuator.
  • the attenuated laser is divided into two laser beams through the diffraction beam splitting lens unit.
  • the power of the two laser beams is equal.
  • the two laser beams pass through The focusing lens unit focuses on the surface of the workpiece to be carved into a cone; and the motion drive controller controls the motion driver to drive the movement of the workpiece to be carved into a cone.
  • the grooves uniformly distributed on the conical surface in a pattern are formed by performing the following operations: fixing the two ends of the workpiece to be carved to a slide rail and a fixing device respectively; a laser controller controls the laser to emit a laser, the power of the laser is 30W, the wavelength is 10600nm, the laser is focused onto the surface of the workpiece to be carved through a lens group, the lens group includes a first concave lens, a first convex lens and a second concave lens, the first concave lens and the first convex lens are used to expand the diameter of the laser beam to a first diameter, the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece to be carved to form a light spot, the diameter of the light spot is 45 ⁇ m; and a motion drive controller controls the motion driver to drive the workpiece to be carved to move.
  • the spatial intensity distribution of the laser emitted by the LITT circumferential ablation probe is obtained by obtaining the signal output by the laser measurement sensor and generating a specific orientation of the laser emitted by the LITT circumferential ablation probe.
  • Polarity intensity wherein the LITT circumferential ablation probe is connected to a helium-neon laser with a laser wavelength of 632.8nm, and a slit diaphragm is provided between the laser measurement sensor and the LITT circumferential ablation probe, so The slit size of the slit diaphragm is 0.3mm; and the motion drive controller controls the motion driver to drive the diaphragm and the laser measurement sensor to perform circumferential and axial movements along the tapered surface of the LITT circumferential ablation probe. to obtain the spatial intensity distribution of the laser light emitted by the LITT circumferential ablation probe, wherein the aperture and the laser measurement sensor are fixedly connected to the motion driver.
  • Another aspect of this specification provides a method for preparing a fiber Bragg grating (FBG) sensor, which is characterized in that the method includes: fixing the raw material for preparing the FBG sensor to a fixing device, and the fixing device is fixedly connected to a motion driver ;
  • the laser controller controls the laser to emit laser, and the laser passes through the beam correction device, the slit diaphragm, the ultraviolet coating lens and the phase mask in sequence, and generates strip-shaped light spots on the surface of the raw material; and the motion drives the controller
  • a motion driver is controlled to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG sensor.
  • the laser is an excimer pulse laser with a characteristic wavelength of 248 nm
  • the laser generated by the laser is a rectangular flat-top beam with a central wavelength of 248 nm and a pulse duration of 15 ns.
  • the beam correction device includes two 248nm characteristic wavelength excimer laser 45° line mirrors
  • the slit diaphragm includes a 4.5mm width adjustable mechanical slit device
  • the UV-coated lens includes 245 -440nm characteristic wavelength UV-coated fused silica plano-convex cylindrical lens
  • the phase mask includes ultraviolet irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask
  • the strip-shaped light spot has a width of 20mm and a height of 32.4 ⁇ m.
  • MFD
  • a medical treatment device including: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object to generate a magnetic resonance image; laser interstitial thermotherapy (LITT) ) device, including a LITT probe that is close to the target object and treats the target object by emitting laser light based on the magnetic resonance image; and a fiber Bragg grating (FBG) sensor configured to Obtain the temperature of the target object, wherein the FBG sensor is prepared according to the above method of preparing an FBG sensor.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermotherapy
  • FBG fiber Bragg grating
  • the FBG sensor is close to the target object and determines a temperature change of the target object, wherein the temperature change of the target object is based on the acquired thermal sensitivity S FSG of the FBG, by adjusting the Bragg wavelength drift ⁇
  • the relationship between S and temperature change ⁇ T is determined by calibration.
  • the relationship between the Bragg wavelength shift ⁇ S and the temperature change ⁇ T is obtained by placing the FBG sensor in a temperature controller, the temperature of the temperature controller changes intermittently, and at the same time, the amplified spontaneous The radiation (ASE) laser passes through the circulator and reaches the FBG sensor.
  • the reflection signal of the FBG sensor enters the telecommunications spectrum analyzer through the circulator.
  • the telecommunications spectrum analyzer monitors the reflection spectrum of the FBG sensor to determine .
  • OCT optical coherence tomography
  • the light beam deflection unit includes a needle core and a hard cladding located on the outer periphery of the needle core.
  • the beam deflection unit includes an oblique The beveled end surface is coated with a metal plating layer.
  • the first lens is a coreless lens
  • the focal length and spot size of the OCT probe are related to the length of the coreless lens and the focal length and spot size of the OCT probe.
  • the second lens is a slightly plano-convex spherical cylindrical lens
  • the starting end of the slightly plano-convex spherical cylindrical lens along the axial direction is a plane
  • the end is a sphere
  • the angle of the plane is 0° or 8°
  • the curvature of the sphere is -1.8 mm
  • the cylindrical diameter of the slightly plano-convex spherical cylindrical lens is 560 ⁇ m.
  • the beam deflection unit has a truncated axial cylinder length of 5 ⁇ m.
  • the OCT probe further includes a spring torsion coil disposed at the front end of the OCT probe; an optical sleeve housing the first lens, the second lens, the beam deflection unit and the spring torsion coil. in the optical sleeve; and a filling body filled inside the optical sleeve to fix the first lens, the second lens, and the beam deflection unit relative to the optical sleeve.
  • a medical treatment apparatus comprising: a magnetic resonance imaging (MRI) device, configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device, comprising a LITT probe, based on the magnetic resonance image, the LITT probe approaches the target object and treats the target object by emitting laser; and an optical coherence tomography (OCT) device, configured to image the target object, the OCT device comprising the above-mentioned OCT probe.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermal therapy
  • OCT optical coherence tomography
  • the medical treatment device includes: a magnetic resonance imaging (MRI) device configured to image a specific area including a target object and generate a magnetic resonance image; a laser interstitial thermal therapy (LITT) device including a LITT probe based on the The magnetic resonance image, the LITT probe is close to the target object and treats the target object by emitting laser; and a temperature measurement element configured to obtain the temperature of a specific position on the edge of the target object, the The specific position is the farthest position from the LITT probe on the edge of the target object.
  • MRI magnetic resonance imaging
  • LITT laser interstitial thermal therapy
  • the temperature measurement element includes a LITT photon temperature measurement probe.
  • the medical treatment device further includes a processing module configured to, when the temperature measured by the temperature measuring element exceeds the preset temperature range, based on the measured temperature and the preset temperature range. The difference between the temperature ranges determines the target laser output dose value of the LITT device so that the temperature measured by the temperature measuring element is within the preset temperature range.
  • the medical treatment device further includes a laser power attenuator configured to adjust the current laser output dose value to the target laser output dose value.
  • the laser power attenuator dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
  • the preset temperature range is 46 ⁇ 1°C.
  • the LITT probe is a LITT lateral ablation probe or a LITT circumferential ablation probe.
  • the LITT circumferential ablation probe is disposed at the equivalent center of the target object, and the temperature measurement element is disposed on the edge of the target object farthest from the LITT circumferential ablation probe.
  • the distance between the LITT circumferential ablation probe and the temperature measuring element is equal to or close to the equivalent radius of the target object.
  • the LITT lateral ablation probe is disposed on one edge of the target object, and the temperature measurement element is disposed on the edge of the opposite side of the target object at a distance from the LITT lateral ablation probe. At the farthest position of the probe, the distance between the LITT lateral ablation probe and the temperature measurement element is equal to or close to the equivalent diameter of the target object.
  • the medical treatment apparatus further comprises an optical coherence tomography (OCT) device configured to image the target object and generate an OCT image.
  • OCT optical coherence tomography
  • the OCT device includes an OCT probe that emits a light signal to the target object to image the target object during treatment, and the OCT probe emits a light signal.
  • the optical signal has two different central wavelengths.
  • the medical treatment device further includes a first driving device coupled to the LITT probe and controlling the translational movement and rotational movement of the LITT probe; and a second driving device coupled to the LITT probe. temperature measuring element, and control the translational movement of the temperature measuring element.
  • the first driving device includes a first translation cable and a first rotation cable, and a first translation control mechanism and a first rotation control mechanism, wherein the first translation cable and the first rotation control mechanism
  • the rotation cables are respectively connected to the first translation control mechanism and the first rotation control mechanism.
  • the first translation control mechanism and the first rotation control mechanism are connected to the LITT probe. Through the first translation cable and The first rotation cable controls the translational movement and rotational movement of the LITT probe respectively.
  • the second driving device includes a second translation cable; and a second translation control mechanism, wherein the second translation cable is connected to the second translation control mechanism, and the second translation A control mechanism is connected to the temperature measuring element and controls the translational movement of the temperature measuring element through the second translation cable.
  • Figure 1 is a medical treatment system according to some embodiments of the present specification.
  • 2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
  • 3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
  • 4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
  • FIG. 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
  • FIG. 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
  • Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
  • Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
  • Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
  • Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
  • FIG. 11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
  • Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
  • Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
  • Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
  • Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
  • Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
  • Figure 17 is a schematic diagram of a medical treatment device according to other embodiments of this specification.
  • Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
  • Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
  • FIG. 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of the present specification.
  • FIG. 1 is a diagram showing a medical treatment system according to some embodiments of the present specification.
  • the medical treatment system 100 is used for medical diagnosis and/or treatment of target objects.
  • the target object may include biological objects (such as human body, animals, etc.).
  • the target object may include the human body or specific parts thereof, such as the head, and/or tissues to be treated, lesions (such as brain tumors and epileptic lesions), etc., or combinations thereof.
  • MRg-LITT magnetic resonance guided laser interstitial thermal therapy
  • MRI magnetic resonance imaging
  • the medical treatment system 100 is not limited to MRg-LITT, and may also be other types of treatment systems, such as MRg microwave treatment, etc.
  • the medical treatment system 100 includes an MRI device 110, a LITT device 120, a temperature measurement element 130, a control device 140, a terminal 150, and an optical coherence tomography (OCT) device (not shown in the figure). ).
  • OCT optical coherence tomography
  • the MRI device 110 is configured to scan a specific area containing a target object and generate an MRI image.
  • the MRI device 110 may be an MRI scanner.
  • the MRI scanner includes a magnet module and a radio frequency (RF) module.
  • the magnet module may include a main magnetic field generator and/or a gradient magnetic field generator.
  • the main magnetic field generator may include a main magnet that generates a static magnetic field B0 during an MRI scan.
  • the main magnet may be a permanent magnet, a superconducting electromagnet, a resistive electromagnet, etc.
  • the gradient magnetic field generator may generate a magnetic field gradient in the X, Y and/or Z directions.
  • the X direction may also be referred to as a readout (RO) direction
  • the Y direction may also be referred to as a phase encoding (PE) direction
  • the Z direction may also be referred to as a slice selection (SS) direction.
  • the gradient magnetic field may encode spatial information of the target object.
  • the RF module may include an RF transmitting coil and/or a receiving coil.
  • the RF transmitting coil may transmit an RF signal (or radio frequency pulse) to excite a region of interest and generate an MRI signal.
  • the RF receiving coil may receive an echo signal emitted by the region of interest.
  • the RF signal may be a 30° pulse signal, a 40° pulse signal, a 60° pulse signal, etc.
  • the MRI device 110 may process the MRI signals to generate an MRI image, which may represent anatomical structure information of a specific region of the target object.
  • the functionality, size, type, geometry, location, and number of magnet modules and/or RF modules may be determined or changed based on one or more specific conditions.
  • RF coils can be divided into body coils and local coils based on differences in function and size.
  • the body coil may be configured as a birdcage coil, a transverse electromagnetic coil, a saddle coil, or the like.
  • the local coils may include phased array coils, loop coils, etc.
  • the local coils may include Holmhertz head coils.
  • the Holmhertz head coil can create a small-scale uniform magnetic field in the patient's head area, send RF signals and receive corresponding head MRI signals.
  • the head MRI signal can be used to image the patient's head to generate a head MRI image.
  • the MRI device 110 can also acquire thermal image data from the MRI scanner for magnetic resonance thermography (MRTI). Based on the thermal image data, a thermal image is reconstructed.
  • the thermal image may represent temperature changes in a specific area containing the target object.
  • each pixel/voxel in the thermal image can measure the temperature change at the corresponding location within the specific area.
  • the LITT device 120 is configured to generate laser light and utilize the thermal effect of the laser light to treat, eg, ablate, the target object. Based on the above-mentioned MRI images and/or thermal images, the location and size of the target object (eg, tumor) can be determined, thereby effectively and controllably guiding the LITT device 120 to emit laser light to perform thermal therapy on the target object.
  • the target object eg, tumor
  • the LITT device 120 includes a laser, a LITT probe, and a channel (such as an optical fiber) and an interface connecting the laser and the LITT probe.
  • the laser can be used to emit laser light.
  • the laser can be a solid laser, a gas laser, a liquid laser, a semiconductor laser, a free electron laser, etc.
  • the wavelength of the laser generated by the laser is within a certain range, for example, the near-infrared region (0.75-2.5 microns ( ⁇ m)).
  • the laser emitted by the laser is transmitted to the LITT probe through the optical fiber and the interface.
  • LITT probe also called LITT probe or LITT diffusion applicator
  • LITT probe is used as a treatment probe to deliver the laser light generated by the laser to the target object to achieve ablation treatment of lesions.
  • the LITT probe includes the probe body.
  • the probe body can be configured in different structures. Under different structures, the position of laser emission is different. Specifically, according to the difference in the exit position, the LITT probe can be divided into a LITT lateral ablation probe and a LITT circumferential ablation probe.
  • a LITT lateral ablation probe refers to a LITT probe in which the laser emission position is located at the end (distal end) of the probe. At this time, the laser emission direction is the same as or at a certain angle with the axial direction of the LITT probe.
  • LITT circumferential ablation probe refers to a LITT probe in which the laser emission position is evenly distributed in the circumference of the probe. At this time, the laser emission direction is the radial direction of the LITT probe, and is evenly dispersed around the circumference of the LITT probe.
  • the type, specific structure and process of the LITT probe reference can be made to other drawings (for example, Figures 6-11) and their descriptions in this application, which will not be described again here.
  • the temperature measurement element 130 is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe.
  • the temperature measuring element 130 can be close to the target object and obtain the temperature of the target object and its surrounding tissues.
  • the LITT device 120 can transfer heat to the target object through the LITT probe in a controlled manner to treat the target object and protect the healthy tissue surrounding the target object.
  • the temperature measurement element 130 may include a thermocouple, a fiber Bragg grating (FBG) sensor, or the like.
  • Thermocouples can directly measure temperature and convert the temperature signal into a thermoelectromotive force signal. The thermoelectromotive force signal can be further converted into the temperature of the object being measured.
  • Thermocouples can include K-type thermocouples, T-type thermocouples, E-type thermocouples, S-type thermocouples, B-type thermocouples, etc.
  • the thermocouple is a K-type thermocouple.
  • the FBG sensor is a sensor in which a specific position of the optical fiber is made into a grating with a periodic distribution of refractive index, and the grating area is used as the sensing area. Light waves of specific wavelengths (Bragg reflected light) are reflected in this grating area.
  • the reflected center wavelength signal is related to the grating period and the effective refractive index of the fiber core.
  • the control device 140 is used to control one or more components of the medical treatment system 100 and perform corresponding operations.
  • the control device 140 can generate corresponding instructions based on the components being controlled and the operations that need to be performed.
  • the instructions are conveyed to the controlled component in the form of electrical signals, causing the component to perform corresponding operations.
  • the control device 140 may receive request or command information input through the terminal 150, and the MRI device 110 and/or the temperature measurement element 130 may generate information (eg, images, temperature data, etc.). Based on the above information, the control device 140 may generate control instructions.
  • the control instructions may be sent to the LITT device 120 for treating the target subject.
  • control device 140 may be a microcontroller unit (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on chip (SoC), etc.
  • MCU microcontroller unit
  • CPU central processing unit
  • PLD programmable logic device
  • ASIC application specific integrated circuit
  • SCM single chip microcomputer
  • SoC system on chip
  • the terminal 150 may be used for input/output of information (eg, images, data, etc.).
  • the terminal 150 may include a computer, a mobile device (eg, a mobile phone, a tablet, a laptop), etc., or any combination thereof.
  • the terminal 150 may include a wearable device, a virtual reality device, an augmented reality device, etc., or any combination thereof.
  • Wearable devices include bracelets, glasses, helmets, watches, etc., or any combination thereof.
  • Virtual reality devices and/or augmented reality devices include virtual reality helmets, virtual reality glasses, virtual reality goggles, augmented reality helmets, augmented reality glasses, augmented reality goggles, etc., or any combination thereof.
  • virtual reality devices and/or augmented reality devices may include Google Glass TM , Oculus Rift TM , Hololens TM , Gear VR TM , etc.
  • terminal 150 may be part of control device 140.
  • the OCT device uses low-coherence interference of a broadband light source to image the target object and generate high-resolution (e.g., micrometer-level) and/or ultra-depth OCT images.
  • the OCT device includes a time-domain optical coherence tomography (TDOCT) device, a spectral domain optical coherence tomography (SDOCT) device, and/or a swept-frequency optical coherence tomography (SSOCT) device.
  • TDOCT time-domain optical coherence tomography
  • SDOCT spectral domain optical coherence tomography
  • SSOCT swept-frequency optical coherence tomography
  • the OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting each component.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of imaging.
  • the OCT probe is used to emit light emitted by the light source to a target object and receive light reflected by the light source.
  • the low-coherence light emitted by the light source can be divided into reference light and sample light (emitted by the OCT probe). Each interferes through the interference component after being reflected by the reference mirror and reflected (or retroreflected) by the tissue of the target object. Based on the interference spectrum formed by the interference, the OCT device (for example, the optoelectronic system therein) can obtain depth information of the structure of the target object.
  • an OCT image of the target object can be generated.
  • the OCT image is a two-dimensional or three-dimensional image.
  • the OCT device can provide pathological imaging. Combined with the LITT device, it can detect the cancerous pathological residue of the ablation lesion in real time, and perform rapid supplementary ablation on the remaining cancerous pathological imaging of the ablation lesion margin, so that the canceration residue and recurrence can be eliminated. The possibility is reduced to a minimum.
  • Each device or component of the medical treatment system 100 may be a local device or component or a remote device or component. Each device or component is connected in one or more various ways.
  • the control device 140 may be a remote device, and the LITT device 110 and the MRI device 120 may be connected to the control device 140 through a network.
  • the control device 140 may be a local device, and the LITT device 110 and the MRI device 120 may be directly connected to the control device 140 .
  • terminal 150 may be connected to control device 140 directly or through a network.
  • the network may include any suitable network that facilitates the exchange of information and/or data with the medical treatment system 100 .
  • the network may be and/or include a public network (eg, the Internet), a private network (eg, a local area network (LAN), a wide area network (WAN)), a wired network (eg, an Ethernet network), a wireless network (eg, an Ethernet network) (e.g., 802.11 networks, Wi-Fi networks), cellular networks (e.g., Long Term Evolution (LTE) networks), Frame Relay networks, virtual private networks (“VPNs”), satellite networks, telephone networks, routers, hubs, switches, servers Computer and/or any combination thereof.
  • a public network eg, the Internet
  • a private network eg, a local area network (LAN), a wide area network (WAN)
  • a wired network eg, an Ethernet network
  • a wireless network e.g., an Ethernet network
  • cellular networks e.g., Long Term Evolution (LTE) networks
  • Frame Relay networks e.g., virtual private networks (“VPNs”), satellite networks, telephone networks
  • the network may include a cable network, a wired network, a fiber optic network, a telecommunications network, an intranet, a wireless local area network (WLAN), a metropolitan area network (MAN), a public switched telephone network (PSTN), a BluetoothTM network , ZifengTM network, near field communication (NFC) network, etc., or any combination thereof.
  • WLAN wireless local area network
  • MAN metropolitan area network
  • PSTN public switched telephone network
  • BluetoothTM network ZifengTM network
  • NFC near field communication
  • 2A-2D are exemplary structural diagrams of medical treatment devices according to some embodiments of the present specification.
  • the medical treatment device 200 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 200 may include a support fixed platform 201, an MRI device 202, a head coil 203, a LITT device (not shown in the figure), an OCT device (not shown in the figure), and a temperature measurement element (Fig. (not shown in the figure), cooling equipment (not shown in the figure), driving device 204, interface platform 205, control relay platform 206, integrated component 207, control device 208, and terminal 209.
  • a support fixed platform 201 an MRI device 202, a head coil 203, a LITT device (not shown in the figure), an OCT device (not shown in the figure), and a temperature measurement element (Fig. (not shown in the figure), cooling equipment (not shown in the figure), driving device 204, interface platform 205, control relay platform 206, integrated component 207, control device 208, and terminal 209.
  • the support and fixation platform 201 also called a treatment bed, is used to support and/or fix the patient to prevent displacement of the patient or its specific parts during treatment.
  • the support and fixed platform 201 can move (eg, translate, tilt, rotate, etc.) based on control instructions issued by the control device 208 to adjust the patient's posture layout during medical diagnosis and/or treatment.
  • the support fixed platform 201 can translate or tilt based on the control instructions issued by the control device 208 during the MRI scanning and imaging process to provide a better scanning position reference for the MRI.
  • the MRI device 202 is used to image a specific area including a target object (e.g., a tumor in the patient's brain) to generate an MRI image.
  • the MRI image may be a real-time MRI image or a non-real-time MRI image.
  • the MRI image may include a three-dimensional image or multiple two-dimensional images (e.g., cross-sectional, coronal, and sagittal images) to characterize information about the target object in three-dimensional space (e.g., position and size, etc.).
  • the information about the target object in three-dimensional space provided by the MRI image can be used to plan the path for the LITT probe, OCT probe, and/or temperature measuring element to pass through human tissue to reach the target object before treatment (referred to as needle insertion planning).
  • the information about the target object in three-dimensional space provided by the MRI image can also be used to guide the LITT probe, OCT probe, and/or temperature measuring element to enter human tissue along the planned path and reach the target object during treatment (referred to as needle insertion guidance).
  • the MRI image may be displayed on the terminal 209.
  • a user such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe based on the MRI image through the terminal 209 (e.g., physical elements such as a touch screen, mouse, and keyboard on the terminal 209).
  • the system may also automatically perform needle insertion planning and guidance of the LITT probe based on the MRI image.
  • the MRI device 202 can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image.
  • the thermal image can be registered with the MRI image, and simultaneously represents the anatomical structure information of the specific area containing the target object and the temperature change information of the corresponding location.
  • the head coil 203 is used to provide deeper head MRI signals.
  • head coil 203 is a Holmhertz magnetic coil.
  • the target object eg, a tumor
  • the head coil 203 can transmit RF signals and receive head MRI signals.
  • the head MRI signal collected by the head coil 203 has a higher signal-to-noise ratio (SNR) than the MRI signal collected by the MRI device 202 .
  • SNR signal-to-noise ratio
  • the head coil 203 may be coupled to the MRI device 202 through an interface to generate more accurate head MRI images.
  • head coil 203 can acquire head thermal image data for head MRTI. Based on the head thermal image data, a thermal image of the patient's head can be reconstructed. In some embodiments, the head coil 203 can also support and fixate the patient's head.
  • the LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object.
  • the LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe.
  • the laser may include a tunable laser diode and/or a non-tunable laser diode.
  • the laser power of the tunable laser diode is tunable within a specific range, for example, 0W-500W, 10-250W, 50-150W, etc.
  • the laser power of the non-tunable laser diode is a specific value, for example, 10W, 12W, 15W, 20W, 30W, 60W, 100W, 150W, etc.
  • the LITT device includes a LITT probe displacement controller 210 for controlling the displacement of the LITT probe.
  • the LITT probe displacement controller 210 controls the LITT probe to pass through the needle insertion channel fixedly provided on the interface platform 206, pass through the patient's skull, enter the skull, and reach the target according to the needle insertion planning and needle insertion guidance. The location of the target object.
  • the interface platform 206 is fixed to the patient's head.
  • the medical treatment device 200 may include a displacement sensor (not shown in the figure) for real-time feedback of displacement data of the LITT probe during the needle insertion process.
  • the displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc.
  • the displacement sensor may be connected to the LITT probe.
  • the displacement sensor may be disposed on the interface platform 206 .
  • the laser light emitted by the laser is processed by the optical path relay processing device 211 and then transmitted to the LITT probe.
  • the optical path relay processing device 211 can adjust the parameters of the laser (for example, power, frequency, etc.). For example, the optical path relay processing device 211 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment.
  • the optical path relay processing device 211 is provided on the control relay platform 204 .
  • the OCT device Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images.
  • the OCT image is a real-time OCT image, and can also be a non-real-time OCT image.
  • the OCT device includes a light source, an OCT probe, an interference component, and optical fibers and interfaces connecting the components.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of imaging.
  • the exemplary structure of the OCT probe can refer to other drawings (e.g., Figure 15) and their descriptions in this application, and will not be repeated here.
  • the OCT device may be a dual-mode OCT, and its light source may generate optical signals with two different parameters (bandwidth, central wavelength).
  • the dual-mode OCT uses an optical signal with a central wavelength of 840 nm over a 160 nm bandwidth, and a central wavelength of 1300 nm over a 100 nm sweep range.
  • Dual-mode OCT can provide pathological imaging with a resolution close to 1 ⁇ m and a depth of cm.
  • the optical fiber slip ring device 212 can be used to ensure uninterrupted transmission of the optical signal.
  • a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device.
  • the optical fiber slip ring device 212 may be disposed on the control relay platform 204 .
  • the temperature measuring element is used to measure the temperature of the target object or its surrounding tissue and/or the LITT probe.
  • Temperature measuring elements can include thermocouples (such as K-type thermocouples), FBG sensors, etc.
  • the FBG sensor is prepared using specially prepared raw materials.
  • the raw material must meet certain parameters.
  • the above-mentioned raw materials are irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), so that the refractive index of the optical fiber core is periodically modulated.
  • Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at specific wavelengths determined by certain phase matching conditions.
  • the reflected wavelength is called the Bragg wavelength of the FBG.
  • the phase matching condition called the Bragg condition, ultimately forms the FBG sensor.
  • the FBG sensor can be used for real-time monitoring of interstitial tissue (eg, target object and its surrounding tissue) and LITT probe (distal) temperature during diffuse laser ablation irradiation.
  • interstitial tissue eg, target object and its surrounding tissue
  • LITT probe distal temperature during diffuse laser ablation irradiation.
  • Cooling equipment is used to control the temperature of the LITT probe. Since the LITT probe emits laser light and uses the thermal effect of the laser to treat the target object, the temperature of the LITT probe will increase as the treatment time increases during the treatment process. Excessive temperature will not only affect the normal operation of the probe, but also damage normal human tissues and may cause postoperative sequelae.
  • the cooling device delivers a specific cooling medium (for example, CO 2 gas) to the distal end of the LITT probe through the cooling channel 214 to cool down the LITT probe.
  • the cooling device includes a cooling source (not shown), a cooling control element 213 and a cooling channel 214 .
  • the cooling source is used to store the cooling medium.
  • the cooling medium may be CO2 gas.
  • the cooling source may be a CO2 gas source tank for storing CO2 gas.
  • the cooling control element 213 can control the on and off of the cooling source, as well as the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas), etc.
  • the above-mentioned LITT probe, OCT probe, temperature measurement element and/or cooling channel can be integrated into one body to form an integrated probe 224 that integrates diagnosis and treatment (hereinafter referred to as integrated probe 224).
  • the temperature measuring element and the LITT probe can be integrated into one body to form the integrated probe 224 .
  • the above-mentioned OCT probe can be integrated with the temperature measurement element and the LITT probe to form an integrated probe 224 .
  • the above-mentioned LITT probe, OCT probe, temperature measurement element and cooling channel can be integrated into one body to form the integrated probe 224 .
  • the drive device 204 is used to drive the LITT probe (e.g., the integrated probe 224) to move to reach the location of the target object (needle insertion) or away from the location of the target object (withdrawal).
  • the movement may include linear translation and rotation.
  • the drive device 204 includes a drive motor, a cable, and a motion control mechanism.
  • the LITT probe is physically connected to the motion control mechanism.
  • the force output by the drive motor can be transmitted to the integrated probe 224 to control its movement.
  • the cable includes a translation cable 215 and a rotation cable 216.
  • the motion control mechanism includes a translation control mechanism 217 and a rotation control mechanism 218.
  • the translation control mechanism 217 is used to control the translation movement of the integrated probe 224.
  • the rotation control mechanism 218 is used to control the rotation movement of the integrated probe 224.
  • the translation cable 215 and the rotation cable 216 are connected to the translation control mechanism 217 and the rotation control mechanism 218, respectively.
  • the cables (such as the translation cable 215 and the rotation cable 216) are specific silk threads with high rigidity and low elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT probe movement.
  • the drive motor can drive the translation cable 215 and/or the rotation cable 216 to move as required, and control the translation and/or rotation of the integrated probe 224 via the translation control mechanism 217 and/or the rotation control mechanism 218. Movement to achieve precise motion control of the two degrees of freedom of the LITT probe (or integrated probe 224).
  • the translation control mechanism 217 and the rotation control mechanism 218 may be provided on the interface platform 205 .
  • Interface platform 205 may carry one or more components or elements of medical treatment device 200 .
  • the mounted components or elements include the needle entry channel of the LITT probe, a displacement sensor, a motion control mechanism (such as a translation control mechanism 217 and a rotation control mechanism 218), etc.
  • interface platform 205 may be a biaxial stereoscopic frame, as shown in the figure.
  • the interface platform 205 can be fixed to the patient's head (skull) and maintain a stable connection with the patient's head without relative displacement.
  • the components or elements carried by the interface platform 205 can be fixedly connected to the biaxial three-dimensional frame.
  • the LITT probe (the above-mentioned integrated probe 224) can enter the patient's skull through the needle insertion channel provided by the interface platform 205 through the needle insertion path, and accurately reach the location of the target object.
  • Control relay platform 206 integrates mid-stage or relay control of one or more components or elements of medical treatment device 200 .
  • the control relay platform 206 integrates the above-mentioned LITT probe displacement controller 210, optical path relay processing device 211, OCT optical fiber slip ring 212, cooling control element 213, and some components of the driving device 204, such as a driving motor.
  • a packaging box is provided on the control relay platform 206.
  • the LITT probe displacement controller 210, the optical path relay processing device 211, the OCT optical fiber slip ring 212, and the cooling control element 213 are arranged in the packaging box.
  • 5 channels are introduced in the packaging box, including OCT probe channel 219 (optical fiber), LITT probe channel 220 (optical fiber), cooling channel 214, temperature measurement element control cable channel 221 and displacement sensor cable Channel 222.
  • OCT optical fiber slip ring 212 is connected to the OCT probe channel 219;
  • the optical path relay processing device 211 is connected to the LITT probe channel 220 and the temperature measurement element control cable channel 221;
  • the cooling control element 213 is connected to the cooling channel 214;
  • the connector 210 is connected to the displacement sensor cable channel 222.
  • the integrated component 207 is used to integrate signal control cables, optical channels, cooling channels, etc. of the medical treatment device 200 .
  • the integrated component 207 can integrate the OCT probe channel 219, the LITT probe channel 220, the cooling channel 214 and the temperature measurement element control cable channel 221, etc., for example, mechanical coupling .
  • the integrated component 207 includes an integrated pipeline 223 that can accommodate an OCT probe channel 219, a LITT probe channel 220, a cooling channel 214, and a temperature measuring element control cable channel 221.
  • the integrated pipeline 223 may be connected to the integrated probe 224 , for example, sealingly connected to the housing of the integrated probe 224 .
  • the control device 208 may be used to control one or more components of the medical treatment device 200 and perform corresponding operations.
  • the control device 208 can generate corresponding instructions based on the components being controlled and the operations that need to be performed.
  • the instructions are conveyed to the corresponding component in the form of electrical signals, causing the component to perform corresponding operations.
  • the control device 208 integrates an OCT imaging control module, a LITT treatment control module, a temperature measurement element temperature control module, a head coil imaging registration module, a cooling system control module, and a LITT probe position sensing control module.
  • the terminal 209 can display information related to each component in the medical treatment device 200 and the patient in the form of images, data, etc.
  • the terminal 209 can display the MRI image of the target object, the thermal image, the registration image of the MRI image and the thermal image, the OCT image, the temperature information measured by the temperature measurement element, and the cooling information of the LITT probe by the cooling device.
  • terminal 209 may also receive user-entered information.
  • Information input through the terminal 209 may include images, numbers, text, voice, etc.
  • the user can input one or more operation instructions through the terminal 209.
  • the operation instructions may include instructions for adjusting the patient's body position layout, operating mode/parameter setting instructions for the MRI equipment 202, head coil 203, LITT equipment (such as LITT probe), OCT equipment (such as OCT probe), cooling equipment, etc. , LITT probe needle path planning instructions during treatment, etc.
  • Information entered via terminal 209 may be sent to control device 208 .
  • the control device 208 can generate control instructions to control the corresponding device or component to perform corresponding operations.
  • the terminal 209 may be or include a computer, a mobile phone, a tablet, a console, etc.
  • MRI compatible refers to the component's ability to be used in an MRI environment.
  • the operation of MRI-compatible components will not cause significant interference to MRI.
  • specific environments for example, 0.5T, 0.75T, 1T, 1.5T, 2.0T, 3.0T, etc.
  • the above There is no danger in the operation of the components.
  • 3A and 3B are structural schematic diagrams of an exemplary driving device according to some embodiments of this specification.
  • the driving device 300 includes a power input terminal 301 , cables 302 and 303 , and a power output terminal 304 .
  • the power output 304 is connected to the LITT probe (or integrated probe 224).
  • the power input from the power input terminal 301 can be transmitted to the power output terminal 304 to drive the LITT probe (or integrated probe 224) to move.
  • the power output end 301 may be a driving motor.
  • Cables 302 and 303 are respectively translation cables and rotation cables, respectively controlling the translation movement and rotation movement of the LITT probe (or integrated probe 224).
  • the driving device 300 additionally includes driving knobs 305 and 306 .
  • the drive knob 305 and the cable 303 are connected through two meshed bevel gears 307 and 308.
  • Two meshed bevel gears 307 and 308 constitute a bevel gear transmission mechanism. Therefore, by rotating the drive knob 305, the cable 303 can also be driven to move, thereby controlling the movement (for example, rotational movement) of the LITT probe (or integrated probe 224). .
  • the torque can be increased and transmitted, so that a smaller driving torque on the driving knob 305 can drive the movement of the cable 303.
  • the drive knob 306 and the cable 302 are also connected through two meshing bevel gears.
  • the driving knobs 305 and 306 can be manually controlled to drive the movement of the cables 303 and 302 respectively, thereby controlling the movement of the LITT probe (or integrated probe 224) as a supplement to the motor driving method, and at the same time, Have better flexibility.
  • 4A-4C are structural schematic diagrams of exemplary translation control mechanisms and/or rotation control mechanisms according to some embodiments of this specification.
  • the figure shows the power output end 304 at different viewing angles.
  • the power output end 304 includes a translation control mechanism and a rotation control mechanism.
  • the translation control mechanism and the rotation control mechanism directly control the translation movement and rotation movement of the LITT probe (or integrated probe 224) respectively.
  • the rotation control mechanism includes a set of timing belt drive assemblies 403 .
  • the timing belt drive assembly 403 connects the LITT probe channel 404 and the rotation cable.
  • the LITT probe (or integrated probe 224) is fixedly disposed in the LITT probe channel 404.
  • the displacement of the rotating cable is converted by the intermediate element (for example, bevel gear combination, worm gear combination), driving the synchronous belt transmission assembly 403 to rotate, thereby causing the LITT probe (or integrated probe 224 ) to rotate.
  • This synchronous belt transmission assembly 403 completes motion control of the LITT probe (or integrated probe 224) at a certain rotation speed through a specific reduction ratio.
  • the translation control mechanism includes a worm gear assembly 401 and a synchronous belt transmission assembly 402. As shown in Figures 4B and 4C, the displacement of the translation cable changes the input shaft orientation through the worm gear assembly 401 and is transmitted to the synchronous belt transmission assembly 402 to realize translation of the LITT probe (or integrated probe 224). At the same time, a certain self-locking effect can also be achieved to make the LITT probe (or integrated probe 224) more stable and free from external force interference.
  • the translation control mechanism and the rotation control mechanism can also be implemented through a gear set transmission mechanism.
  • FIG. 5 is an exemplary structural diagram of a control device according to some embodiments of this specification.
  • control device 208 includes an OCT imaging control module 501, a LITT treatment control module 502, a temperature measurement element temperature control module 503, a head coil imaging registration module 504, a cooling system control module 505, and a LITT probe position sensing module.
  • the OCT imaging control module 501 is used to control OCT imaging.
  • the OCT imaging control module 501 can control the OCT device to emit optical signals and set imaging parameters (for example, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.) by generating instructions.
  • the OCT imaging control module 501 can also acquire the generated pathological diagnosis signal to generate an OCT image.
  • the optical signal emitted by the OCT equipment is transmitted to the OCT probe through the optical fiber slip ring device 212.
  • the LITT treatment control module 502 is used to control the LITT probe to treat the target object.
  • LITT treatment control module 502 integrates a laser controller, a tunable laser diode and/or a non-tunable laser diode.
  • the laser controller can control the laser (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT.
  • the LITT treatment control module 502 can control the laser to emit laser, and the emitted laser is transmitted to the LITT probe through the optical path relay processing device 211.
  • the temperature measurement element temperature control module 503 is used to control the temperature measurement element to measure the temperature of the target object and its surrounding tissues and/or the LITT probe.
  • the temperature measurement signal of the temperature measurement element (such as the FBG sensor heat source optical signal or the K-type thermocouple analog temperature control signal) can be transmitted through the optical path relay processing device 211.
  • the head coil imaging registration module 504 is used to control the registration of the imaging of the head coil (such as head MRI image, head thermal image) and the imaging of the MRI equipment (such as MRI image, thermal image), so as to obtain clearer, Images that are accurate and provide temperature information.
  • the imaging of the head coil such as head MRI image, head thermal image
  • the imaging of the MRI equipment such as MRI image, thermal image
  • the cooling system control module 505 is used to control the cooling equipment to cool the LITT probe.
  • the cooling system control module 505 can control the opening and closing of the cooling source and the parameters of the cooling medium (for example, the flow rate and pressure of CO 2 gas) through the cooling control element 213, combined with the temperature of the LITT probe measured by the temperature measuring element. , controls the temperature of the LITT probe to prevent the probe from overheating and damage, and plays a role in protecting the probe.
  • the temperature of the target object and its surrounding tissue measured by the temperature measuring element can also be combined to control the temperature of the healthy tissue surrounding the target object to avoid unnecessary damage.
  • the cooling system control module 505 can control the cooling medium to be recycled through the cooling channel.
  • the LITT probe position sensing control module 506 is used to detect the real-time position of the LITT probe deep into the skull in real time by controlling the LITT probe displacement controller 210 .
  • the LITT probe position sensing control module 506 can also send control signals to the LITT probe displacement controller 210 in real time, issue displacement triggering instructions and receive position feedback processing signals.
  • the displacement triggering instruction is used to trigger the LITT probe displacement controller 210 to control the movement of the LITT probe.
  • the position feedback processing signal is used to judge and decide the subsequent movement of the LITT probe (for example, continue to move forward, adjust direction, retreat, etc.) based on the real-time position of the LITT probe.
  • the drive control module 507 is used to control the drive motor of the drive device 204 to drive the translation cable 215 and/or the rotation cable 216, and control the LITT probe ( Or the translational and/or rotational movement of the integrated probe 224), achieving precise motion control of the two degrees of freedom of the LITT probe (or the integrated probe 224).
  • the support and fixed platform control module 508 is used to control the movement of the support and fixed platform 201 .
  • the support and fixed platform control module 508 controls the movement of the support and fixed platform 201 (for example, translation, tilt, rotation, etc.) by issuing motion control instructions to adjust the patient's posture layout and provide a better scanning position reference for MRI.
  • FIG. 6 is an illustration of two different types of integrated probes in accordance with some embodiments of the present specification.
  • the integrated probe 224 is connected to an OCT probe channel, a LITT probe channel, a cooling channel and a temperature measurement element control cable channel.
  • the above four channels are mechanically coupled through the integrated component 207 and are jointly accommodated in the integrated pipeline of the integrated component 207 .
  • the integrated pipeline is connected to the integrated probe 224 directly or through an interface.
  • the integrated pipeline is connected to the integrated probe 224 through the interface 601 .
  • the interface 601 is provided on the interface platform 205.
  • the two different types of integrated probes may include a LITT lateral ablation integrated probe 610 and a LITT circumferential ablation integrated probe 660.
  • the LITT lateral ablation integrated probe 610 includes a temperature measuring element 611, a CO2 gas supply tube 612, a LITT lateral ablation probe 613 (also called a LITT lateral ablation needle core), an OCT probe 614, and a CO2 gas collection tube 615.
  • the LITT lateral ablation probe 613 in the LITT lateral ablation integrated probe 610 can be prepared by at least two different processes.
  • the LITT circumferential ablation integrated probe 660 includes a temperature measurement element 661, a CO 2 air supply tube 662, a LITT circumferential ablation probe 663 (also called a LITT circumferential ablation needle core), an OCT probe 664, and a CO 2 air collecting tube 665 .
  • LITT circumferential ablation probe 663 also called a LITT circumferential ablation needle core
  • OCT probe 664 an OCT probe 664
  • CO 2 air collecting tube 665 for the specific structure and process of the LITT circumferential ablation probe 663 in the LITT lateral ablation integrated probe 610.
  • Figure 7 shows an exemplary LITT lateral ablation probe prepared by the first process according to some embodiments of the present specification.
  • the LITT lateral ablation probe 700 includes a probe body 710 , a connection surface 720 and a coating 730 .
  • the connection surface 720 is the connection interface between the main body 710 and the plating layer 730 .
  • the probe body 710 is cylindrical. In some embodiments, the end (distal end) of the probe body 710 has a certain inclination angle (that is, the end surface of the probe body 710 and the axis of the probe body 710 form a certain angle, and the included angle is 0-90°, and does not include the endpoints of the range).
  • the probe body 710 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • connection surface 720 uses a diamond film with specific precision (for example, 0.1 ⁇ m, 0.5 ⁇ m, 1 ⁇ m, 2 ⁇ m, 3 ⁇ m, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface of the total reflection lens.
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA,
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
  • the plating layer 730 uses noble metal target plating.
  • the precious metals may include, for example, gold, silver, and platinum group metals.
  • the coating 730 is formed by evaporation coating (for example, resistance heating evaporation coating, electron beam heating evaporation coating, induction heating evaporation coating), sputtering coating (such as magnetron sputtering coating), or ion plating.
  • the coating layer 730 is formed by magnetron sputtering coating on the surface of the connection surface 720 .
  • the plating layer 730 can be a double-layer structure, and the lower layer (near the connection surface 720) is pure silver (for example, 99.99) coated with a specific thickness (for example, 60 nanometers (nm), 80 nm, 100 nm, 120 nm, 140 nm) through magnetron coating. %, 99.999%, 99.9999% or 99.99999% pure silver), the upper layer (away from the connection surface 720) is coated with a specific thickness (for example, 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating. Silicon oxide protective layer.
  • the plating layer 730 may have a single-layer structure, and is coated with pure gold (for example, 99.99%, 99.999%, 99.9999% or 99.99999%) of a specific thickness (for example, 60nm, 80nm, 100nm, 120nm, 140nm) through magnetron coating. pure gold).
  • the plating 730 is at an angle to the axis of the probe body 710 .
  • the angles are, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc.
  • the above pure silver and silicon monoxide coating scheme, combined with the angle of the coating 730, can make the LITT high-power ablation laser reflectivity efficiency as high as 87%.
  • pure silver coating prevents beam leakage through the polished surface, helping to deflect the beam at wider incident angles (i.e. Lower than TIR angle range) compatibility and uniform focusing point, reflectivity, optical path deflection performance and stability are greatly improved compared to TIR.
  • the LITT lateral ablation probe 700 uses a beam with an emission angle of about 81° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
  • the preparation process of the LITT lateral ablation probe 700 includes the following steps:
  • Step S7-1 Smooth the end surface of the main body 710.
  • the end surface of the main body 710 here refers to the connection interface between the main body 710 and the plating layer 730, that is, the connection surface 720.
  • a specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery.
  • TECS technology-enhanced cladding silica
  • a suspension of specific components is applied to the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 710 .
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the end (distal end) of the probe body 710 has a certain inclination angle, that is, the end surface of the probe body 710 forms a certain angle with the axis of the probe body 710 . If the end of the probe body 710 has no inclination angle, that is, the end surface of the probe body 710 is perpendicular to the axis of the probe body 710, a grinding step is also included. By grinding, the end surface of the probe body 710 can be aligned with the axis of the probe body 710. It forms a certain included angle, and the included angle is 0-90°, and does not include the endpoint of this range. Mechanical processing can be used to grind the end surface with a grinding wheel.
  • Step S7-2 Coating the smoothed end surface of the main body 710 to form the LITT lateral ablation probe 700.
  • the end face of the main body 710 is plated with a noble metal target.
  • the coating 730 is formed by magnetron sputtering coating on the end face of the main body 710.
  • the coating 730 can be a double-layer structure, in which case the lower layer (close to the end face) of the double-layer structure is pure silver (e.g., 99.99%, 99.999%, 99.9999% or 99.99999% pure silver) coated with a specific thickness (e.g., 60 nanometers (nm), 80nm, 100nm, 120nm, 140nm) by magnetron coating, and the upper layer (away from the end face) of the double-layer structure is a silicon monoxide protective layer coated with a specific thickness (e.g., 120nm, 130nm, 140nm, 150nm, 160nm, 170nm, 180nm) by magnetron coating.
  • a specific thickness e.g., 120nm, 130nm, 140nm, 150nm, 160n
  • the coating 730 may also be a single-layer structure, in which case it is formed by magnetron coating a specific thickness (e.g., 60nm, 80nm, 100nm, 120nm, 140nm) of pure gold (e.g., 99.99%, 99.9999%, 99.9999% or 99.99999% pure gold).
  • a specific thickness e.g. 60nm, 80nm, 100nm, 120nm, 140nm
  • pure gold e.g., 99.99%, 99.9999%, 99.9999% or 99.99999% pure gold
  • Figure 8 shows an exemplary LITT lateral ablation core prepared by the second process according to some embodiments of the present specification.
  • the LITT lateral ablation probe 800 includes a probe body 810 , a connection surface 820 , and a lens 830 .
  • the connection surface 820 is the connection interface between the main body 810 and the lens 830 .
  • the probe body 810 is cylindrical.
  • the probe body 810 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • connection surface 820 uses a diamond film with specific precision (for example, 0.1 ⁇ m, 0.5 ⁇ m, 1 ⁇ m, 2 ⁇ m, 3 ⁇ m, etc.), and removes a certain numerical aperture (for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA) , 0.41NA, 0.42NA, 0.43NA, 0.44NA, 0.45NA, etc.) special step refractive index multi-mode material core, and a technology-enhanced cladding silica (TECS) hard cladding is set on the periphery as the main material. Then, a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface perpendicular to the end (flat end) of the probe body 810 .
  • a certain numerical aperture for example, 0.35NA, 0.36NA, 0.37NA, 0.38NA, 0.39NA, 0.4NA
  • a certain numerical aperture for example, 0.41NA, 0.42NA,
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 10%-20% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 30%-40% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • the suspension contains 20%-30% synthetic amorphous silica, 10%-20% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 30%-40% H 2 O, 45%-55% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 35%-45% (propane-1,2 -diol). In some embodiments, by mass fraction, the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 55%-65% (propane-1,2 -diol).
  • lens 830 utilizes a sapphire lens.
  • lens 830 includes a right angle (90°), a base angle, and an apex angle.
  • the angle of the top corner can be determined based on the angle of the bottom corner.
  • the right angle, base angle and vertex angle satisfy a certain relationship, for example, the angle of the vertex angle is equal to 90° minus the given angle of the base angle.
  • the main body 810 and the lens 830 are both cylinders, and the lens 830 is a beveled cylinder.
  • the right angle, base angle and vertex angle here are the angles formed by each side of the lens 830 in a two-dimensional image formed from a viewing angle parallel to the oblique plane.
  • the base angle is within a certain angle range. In some embodiments, the base angle is 50°-45°. Correspondingly, the vertex angle is 40°-45°. In some embodiments, the base angle is 52°-47°. Correspondingly, the vertex angle is 38°-43°. In some embodiments, the base angle is 54°-49°. Correspondingly, the vertex angle is 36°-41°. In some embodiments, the base angle is 56°-51°. Correspondingly, the vertex angle is 34°-39°.
  • the length of the right-angled side between the base angle and the right angle of the lens 830 (i.e., the right-angled side forming the base angle), that is, the diameter of the cylindrical lens, is equal to the outer diameter of the probe body 810, which is the technology-enhanced cladding dioxide
  • the outer diameter of the silicon (TECS) hard cladding is equal to the outer diameter of the silicon (TECS) hard cladding.
  • tungsten such as tungsten wire
  • iridium such as iridium wire
  • the downlink tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed.
  • Fire polishing also known as flame polishing, can be done using a flame polishing machine. This process combines the lens and the lens vertex angle within a specific angle range from the horizontal plane (for example, 40°-45°, 38°-43°, 36°-41°, 34°-39°) to improve the LITT lateral Ablation Probe 800 performance.
  • the LITT lateral ablation probe 800 uses a beam with an emission angle of about 78° to uniformly emit controlled laser light to the target object to achieve ablation of the lesion tissue.
  • the lens 830 may also be a beveled hemispherical lens (such as a sapphire hemispherical lens).
  • the diameter of the beveled hemispherical lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, etc.
  • the lens 830 may also be a beveled semi-ellipsoidal lens (such as a sapphire semi-ellipsoidal lens).
  • the long semi-axis of the beveled semi-ellipsoidal lens is, for example, 0.5 mm, 0.6 mm, 0.7 mm, 0.8 mm, 0.9 mm, 1 mm, 1.1 mm, 1.2 mm, etc.
  • the flattening of the beveled semi-ellipsoidal lens is, for example, 1/298, 1/250, 1/200, 1/150, 1/100, 1/50, etc.
  • the preparation process of the LITT lateral ablation probe 800 includes the following steps:
  • Step S8-1 Smooth the end surface of the main body 810.
  • the end surface of the main body 810 refers to the connection interface between the main body 810 and the lens 830, that is, the connection surface 820.
  • the end surface of the main body 810 is perpendicular to the axis of the main body 810 .
  • a specific precision diamond film is used to remove the core of a special step refractive index multi-mode material with a certain numerical aperture, and a technology-enhanced cladding silica (TECS) hard cladding is set as the main material on the periphery.
  • TECS technology-enhanced cladding silica
  • a suspension of specific components is coated on the surface of the silica colloidal base film to form a smooth surface at the end of the probe body 810 .
  • the suspension contains synthetic amorphous silica, H2O , and propane-1,2-diol.
  • the suspension contains 20%-30% synthetic amorphous silica, 20%-30% H 2 O, 45%-55% (propane-1,2 -diol).
  • Step S8-2 Weld the main body 810 and the lens 830 to form the LITT lateral ablation probe 800.
  • the main body 810 and the lens 830 are welded using a specific high-temperature treatment method to establish a stable connection between the lens 830 and the main body 810 .
  • body 810 and lens 830 may be welded by arc welding.
  • high-temperature melting of materials such as tungsten (such as tungsten wire) and iridium (such as iridium wire) can also be used to weld the main body 810 and the lens 830 .
  • tungsten wire or iridium a tungsten wire or iridium wire fire polishing process is selected, that is, the welding surface is fire polished, and finally the LITT lateral ablation probe 800 is formed.
  • Figure 9 illustrates an exemplary LITT circumferential ablation probe in accordance with some embodiments of the present specification.
  • LITT circumferential ablation probe 900 includes probe body 910 .
  • the probe body 910 is composed of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • the diameter (outer diameter) of the needle core is, for example, 550-650 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 560 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 570 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 580 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 590 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 600 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 610 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 620 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 630 ⁇ m. In some embodiments, the diameter (outer diameter) of the needle core is 640 ⁇ m.
  • the thickness of the hard cladding is, for example, 5-30 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 5 ⁇ m. In some embodiments, the hard cladding layer has a thickness of 10 ⁇ m. In some embodiments, the hard cladding has a thickness of 15 ⁇ m. In some embodiments, the hard cladding has a thickness of 20 ⁇ m. In some embodiments, the hard cladding has a thickness of 25 ⁇ m. In some embodiments, the hard cladding has a thickness of 30 ⁇ m.
  • a tapered surface 920 is provided at the distal end of the probe body 910 (the end close to the target object).
  • the diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter.
  • the initial diameter is the sum of the diameter of the needle core and the thickness of the cladding. Exemplarily, the initial diameter is 630 ⁇ m.
  • the preset diameter is the diameter of the distal end of the probe body 910 .
  • the preset diameter is 50-150 ⁇ m. In some embodiments, the preset diameter is 60 ⁇ m. In some embodiments, the preset diameter is 70 ⁇ m. In some embodiments, the preset diameter is 80 ⁇ m. In some embodiments, the preset diameter is 90 ⁇ m.
  • the preset diameter is 100 ⁇ m. In some embodiments, the preset diameter is 110 ⁇ m. In some embodiments, the preset diameter is 120 ⁇ m. In some embodiments, the preset diameter is 130 ⁇ m. In some embodiments, the preset diameter is 140 ⁇ m.
  • Grooves are provided on the tapered surface 920 .
  • the laser light directed to the LITT circumferential ablation probe 900 can be emitted from the groove to treat the target object and achieve ablation of the lesion tissue.
  • the grooves are evenly (dispersed) distributed along the tapered surface 920 in a certain pattern shape (for example, thread shape) and do not overlap with each other. LITT circumferential ablation probe, also known as LITT circumferential diffusion ablation probe.
  • the groove has a certain depth. Exemplarily, the depth of the groove is 5-35 ⁇ m. In some embodiments, the groove has a depth of 10 ⁇ m. In some embodiments, the groove has a depth of 15 ⁇ m. In some embodiments, the groove has a depth of 20 ⁇ m. In some embodiments, the groove has a depth of 25 ⁇ m. In some embodiments, the groove has a depth of 30 ⁇ m.
  • the distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross, as shown in Figure 9), a rhombus grid shape, a honeycomb shape, etc., or combination thereof.
  • the single thread shape, multi-thread cross shape, rhombus grid shape, and honeycomb shape listed above are only specific examples and do not limit the specific distribution pattern of the grooves. It can also be any other reasonable pattern. It is required that the specific distribution shape of the grooves is evenly (dispersed) distributed along the tapered surface 920 and does not overlap.
  • the tapered surface 920 and the evenly distributed grooves arranged in a certain pattern on the tapered surface 920 can be formed by engraving with an optoelectronic device (for example, an optical machine).
  • an optoelectronic device for example, an optical machine
  • the tapered surface 920 and the cross-threaded grooves provided thereon can be carved and formed by the optoelectronic equipment and method described in FIGS. 10 and 11 , respectively.
  • the tapered surface 920 and the groove provided thereon can also be processed by other methods, such as mechanical processing.
  • Figure 10 is a schematic diagram of an exemplary tapered surface processing according to some embodiments of the present specification.
  • the tapered surface 920 is carved and formed by the tapered engraving device 1000 .
  • the cone engraving equipment 1000 includes a terminal 1001, a laser controller 1002, a laser 1003, reflectors 1004-1 and 1004-2, a shutter 1005, a shutter controller 1006, a laser power attenuator 1007, a diffraction beam splitting lens unit 1008, and a focusing lens unit. 1009, slide rail 1010, fixing device 1011, motion driver 1012, and motion drive controller 1013.
  • the terminal 1001 connects to and controls the laser controller 1002, the shutter controller 1006 and the motion drive controller 1013.
  • the laser controller 1002 connects and controls the laser 1003 to emit laser light.
  • the terminal 1101 may be, for example, a computer.
  • Laser 1003 may be a high power CO2 continuous wave laser.
  • Reflectors 1004-1 and 1004-2 can use silver mirrors.
  • Shutter 1005 may be an electric shutter.
  • the shutter controller 1006 is connected to and controls the switch of the shutter 1005 to control the opening and closing of the laser light path.
  • the diffraction beam splitting lens unit 1008 and the focusing lens unit 1009 are used to split the laser beam to form two laser beams and focus them respectively.
  • the focusing lens unit 1009 may be, for example, a zinc selenide lens.
  • the motion drive controller 1013 is connected to and controls the motion driver 1012 to drive the workpiece 1015 to be tapered to move, for example, translation and/or rotation.
  • the process of carving the cone surface 920 by the cone carving device 1000 includes the following steps:
  • Step S10-1 Fix both ends of the workpiece 1015 to be carved to the slide rail 1010 and the fixing device 1011 respectively.
  • the fixing device 1011 is connected to the motion driver 1012 .
  • Fixing device 1011 may be a clamp. The clamp can clamp and fix one end of the workpiece 1015 to be tapered.
  • Step S10-2 Use the terminal 1001 to cause the laser controller 1002 to control the laser 1003 to emit laser.
  • Laser 1003 generates laser light with a specific power and wavelength.
  • the power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the laser generated is 25W. In some embodiments, the power of the laser generated is 30W. In some embodiments, the power of the laser generated is 35W.
  • the wavelength of the laser produced is approximately 10600nm.
  • the laser light is reflected to the shutter 1005 via the mirror 1004-1.
  • Step S10-3 The shutter controller 1006 controls the shutter 1005 to open through the terminal 1001, and the laser is emitted to the laser power attenuator 1007 for power attenuation processing.
  • the laser power attenuator 1007 attenuates the input laser power by a certain proportion, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, etc., that is, performs power attenuation processing. .
  • the laser power output by the laser power attenuator 1007 (that is, the laser power after attenuation processing) is within a certain range, for example, 3-20W.
  • the laser power after attenuation treatment is 6-15W.
  • the laser power after attenuation treatment is 6.6-11.2W.
  • the diffraction beam splitting lens unit 1008 may be a beam splitting lens customized for the laser wavelength.
  • Step S10 - 4 The laser beam after power attenuation processing is split into two laser beams by the diffraction beam splitting lens unit 1008 , and the two laser beams are focused onto the surface of the workpiece 1015 to be coned by the focusing lens unit 1009 .
  • the workpiece 1015 to be tapered includes a fiber core and a hard cladding around the core.
  • the core is made of pure silica material.
  • the hard cladding around the core is made of Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the two laser beams respectively form light spots 1014-1 and 1014-2 on the surface of the workpiece 1015 to be carved.
  • the light spots 1014-1 and 1014-2 are focused on the peripheral hard cladding of the workpiece 1015 to be carved.
  • Step S10-5 Use the terminal 1001 to cause the motion drive controller 1013 to control the motion driver 1012 to drive the movement of the workpiece 1015 to be tapered.
  • the light spots 1014-1 and 1014-2 formed by the laser are engraved on the surface of the workpiece 1015 to be carved with a cone, and finally a conical surface 920 is formed.
  • FIG. 11 is a schematic diagram of processing of exemplary cross-threaded grooves according to some embodiments of the present specification.
  • cross-threaded grooves are carved and formed on the surface of the workpiece 1110 to be carved by the engraving device 1100 .
  • the workpiece 1110 to be carved is a workpiece with a tapered surface 920 that has been processed through the above steps S10-1 to S10-5.
  • the engraving equipment 1100 includes a terminal 1101, a laser controller 1102, a laser 1103, a reflector 1104, a lens group 1005, a slide rail 1106, a fixing device 1107, a motion driver 1108, and a motion drive controller 1109.
  • the terminal 1101 connects and controls the laser controller 1102 and the motion drive controller 1109.
  • the terminal 1101 may be, for example, a computer.
  • the laser controller 1102 connects and controls the laser 1103 to emit laser light.
  • Laser 1103 may be a high power CO2 continuous wave laser.
  • the reflector 1104 may be a silver mirror.
  • Lens group 1005 may include one or more lenses.
  • the one or more lenses include concave lenses and/or convex lenses.
  • the motion drive controller 1109 is connected to and controls the motion driver 1108 to drive the workpiece 1110 to be carved to move, for example, translation and/or rotation.
  • the process of engraving cross-threaded grooves by the engraving device 1100 includes the following steps:
  • Step S11-1 Fix both ends of the workpiece 1110 to be carved to the slide rail 1106 and the fixing device 1107 respectively.
  • the fixation device 1107 is connected to the motion driver 1108 .
  • Fixing device 1107 may be a clamp. The clamp can clamp and fix one end of the workpiece 1110 to be carved.
  • Step S11 - 2 The terminal 1101 enables the laser controller 1102 to control the laser 1103 to emit laser light.
  • the laser generated by the laser 1103 has a specific power and wavelength.
  • the power of the generated laser is, for example, in the range of 20-40W. In some embodiments, the power of the generated laser is 25W. In some embodiments, the power of the generated laser is 30W. In some embodiments, the power of the generated laser is 35W.
  • the wavelength of the generated laser is about 10600nm.
  • the laser 1103 can be a high-power CO2 continuous wave laser.
  • the damage threshold of the workpiece 1110 to be engraved is about 250kW/ cm2 ; for the pulse wave of the high-power CO2 continuous wave laser (for example, a pulse wave of 10ns), the damage threshold of the workpiece 1110 to be engraved is about 1GW/ cm2 .
  • Step S11-3 The laser is focused on the surface of the workpiece 1110 to be carved through the lens group 1105.
  • the laser passes through the lens group 1105 and forms a light spot of specific energy and size on the conical surface of the workpiece 1110 to be carved.
  • the diameter of the light spot is 30-60 ⁇ m.
  • the spot diameter is 35 ⁇ m.
  • the diameter of the light spot is 40 ⁇ m.
  • the spot diameter is 45 ⁇ m.
  • the diameter of the light spot is 50 ⁇ m.
  • the spot diameter is 55 ⁇ m.
  • the energy of the light spot is higher than the irradiance of the surface material ablation of the workpiece 1110 to be carved.
  • the irradiance of the surface material of the workpiece 1110 to be carved is close to the irradiance of glass ablation, which is 3.1 ⁇ 10 5 W/cm 2 .
  • the lens group 1105 may include a first concave lens, a first convex lens, and a second concave lens arranged in sequence.
  • the first concave lens and the first convex lens are used to expand the diameter of the laser beam to the first diameter
  • the second concave lens is used to focus the laser beam of the first diameter onto the surface of the workpiece 1110 to be engraved to form the above-mentioned light spot.
  • Step S11-4 Use the terminal 1101 to cause the motion drive controller 1109 to control the motion driver 1108 to drive the workpiece 1110 to be engraved to move.
  • the light spot formed by the laser engraves on the surface of the workpiece 1110 to be carved, and finally forms grooves distributed in a cross-thread shape on the conical surface of the workpiece 1110 to be carved.
  • an air cooling system can be used to blow the engraved grooves and remove particles (such as dust, impurities) in and around the grooves. Molten materials, etc., keep the surface of the processing area clean.
  • the LITT circumferential ablation probe 900 engraved by the optoelectronic equipment and method described in Figures 10 and 11 has a certain pattern (for example, cross threads) of grooves evenly (diffuse) distributed along the tapered surface 920, so the LITT circumferential
  • the vector light energy distributed to the ablation probe 900 is more evenly distributed, and combined with the temperature measurement mechanism of the above-mentioned temperature measurement element, the ablation of the surrounding tissue is more uniform and complete.
  • the tissue thermal characteristics and thermal damage algorithm based on the LITT circumferential ablation probe 900 the protection of healthy tissue during the operation and the ablation effect of ablation pathology have been significantly improved.
  • Figure 12 is a schematic diagram of vector light energy distribution of a LITT circumferential ablation probe tested according to some embodiments of this specification.
  • the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be tested by the LITT probe polarity testing device 1200 .
  • the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 can be characterized by the polar intensity of the circumferential spatial light distribution of the LITT circumferential ablation probe 900 at different heights.
  • the LITT probe polarity testing device 1200 includes a laser 1201, a fiber coupler 1202, a LITT circumferential ablation integrated probe 1203, an aperture 1204, a laser measurement sensor 1205, a terminal 1206, a motion driver 1207, and a motion drive controller 1208.
  • the laser 1201 may be a helium-neon laser.
  • the helium-neon laser is a helium-neon laser emitting a laser wavelength of 632.8 nm.
  • the aperture 1204 is used to limit the propagation of the light beam.
  • the aperture 1204 is installed in front of the laser measurement sensor 1205 to limit the laser received by the laser measurement sensor 1205, for example, so that the laser measurement sensor 1205 can only receive lasers in a specific direction.
  • the aperture 1204 may be an aperture aperture, a slit aperture, etc.
  • the aperture 1204 may be a slit aperture.
  • the size of the slit aperture i.e., the width of the slit
  • the size of the slit aperture is 0.2 mm. In some embodiments, the size of the slit aperture is 0.3 mm. In some embodiments, the size of the slit aperture is 0.4 mm.
  • the laser measurement sensor 1205 is used to receive laser light and generate a corresponding electrical signal to characterize the intensity of the received laser light. In some embodiments, the laser measurement sensor 1205 may be a circular geometry photodiode laser measurement sensor or other sensors that can measure laser intensity.
  • the terminal 1206 is connected to and controls the laser measurement sensor 1205 and the motion drive controller 1208. The terminal 1206 can be, for example, a computer.
  • the aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207.
  • the motion drive controller 1208 is connected to and controls the motion driver 1207 to drive the aperture 1204 and the laser measurement sensor 1205 to move, for example, translate and/or rotate.
  • the process of testing the uniformity of the vector light energy distribution of the LITT circumferential ablation probe 900 through the LITT probe polarity testing device 1200 includes the following steps:
  • Step S12-1 Obtain the signal output by the laser measurement sensor 1205 through the terminal 1206, and generate the laser polarity intensity in a specific direction.
  • the laser 1201 generates laser light (for example, visible light) and conducts it to the optical fiber coupler 1202 via a spatial optical path (such as an optical fiber).
  • Fiber optic coupler 1202 couples to the LITT probe channel of the LITT circumferential ablation integrated probe.
  • the laser light is transmitted to the LITT circumferential ablation probe 900 and passes through the circumferentially uniformly distributed grooves on the LITT circumferential ablation probe 900 to emit vector light energy in a 360-degree dispersion.
  • the vector light energy is limited by the aperture 1204 and enters the laser measurement sensor 1205.
  • the laser measurement sensor 1205 receives the incident laser and generates a corresponding electrical signal to represent the intensity of the received laser. This intensity is the laser polarity intensity of the aperture 1204 and the laser measurement sensor 1205 in this orientation.
  • Step S12-2 The motion drive controller 1208 controls the motion driver 1207 through the terminal 1206 to drive the aperture 1204 and the laser measurement sensor 1205 to move circumferentially and axially along the tapered surface of the LITT circumferential ablation probe 900 , thereby obtaining the intensity distribution of the laser in the entire space (referred to as spatial intensity distribution).
  • the entire space refers to the circumference (360 degrees) and axial direction (overall length) of the LITT circumferential ablation probe 900 .
  • the motion driver 1207 is controlled by the motion drive controller 1208 to perform rotational circular motion.
  • the aperture 1204 and the laser measurement sensor 1205 are fixedly connected to the motion driver 1207. Therefore, the aperture 1204 and the laser measurement sensor 1205 will make a circle around the LITT circumferential ablation probe 900. Movement, and then based on the method for determining the single-point polarity intensity in the above step S12-1, the circumferential vector light distribution polarity intensity of the LITT circumferential ablation probe 900 is obtained.
  • the motion driver 1207 is used to adjust the positions of the aperture 1204 and the laser measurement sensor 1205 relative to the length direction of the LITT circumferential ablation probe 900 (which can also be referred to as different heights) to obtain the values of the LITT circumferential ablation probe 900 at different heights.
  • the polar intensity of the circumferential vector light is distributed, thereby obtaining the intensity distribution of the laser (vector light) in the entire space.
  • the LITT circumferential ablation probe 900 formed by the photoelectric equipment and method described in Figures 10 and 11 was tested using the methods described in S12-1 and S12-2 above.
  • the vector light energy distribution is very uniform. Therefore, the LITT circumferential ablation probe 900 has better performance and therapeutic effect.
  • Figure 13 is a schematic diagram of temperature measurement using a thermocouple according to some embodiments of this specification.
  • the temperature measurement element (temperature measurement element 611 or 661), such as the thermocouple 1303, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) to Measure the temperature of the LITT probe and/or target object.
  • the integrated probe LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660
  • the thermocouple 1303 may be connected to the power collection module 1302.
  • the power supply collection module 1302 is further connected to the terminal 1301.
  • the power supply acquisition module 1302 provides power to the thermocouple 1303 and transmits the temperature collected during the operation of the thermocouple 1303 to the terminal 1301.
  • Terminal 1301 may be, for example, a computer.
  • the thermocouple 1303 can be a K-type thermocouple, a T-type thermocouple, an E-type thermocouple, etc.
  • the thermocouple 1303 is a K-type thermocouple.
  • the parameters of the K-type thermocouple may be a diameter of 40-60 ⁇ m, a resistance of 46-55 ohms ( ⁇ ), and a measurement accuracy of ⁇ 0.5-2 degrees Celsius (°C).
  • the parameters of the K-type thermocouple are 50 ⁇ m in diameter, 51 ⁇ in resistance, and ⁇ 1.2°C in measurement accuracy.
  • thermocouple 1303 When the LITT probe is working, the thermocouple 1303 is close to the target object. At the same time, the LITT probe emits a laser ablation signal, which will also affect the thermocouple 1303.
  • the thermocouple 1303 is connected to the terminal 1301 through the power supply collection module 1302, and collects and records the temperature changes of the target object and/or LITT probe in real time. Thermocouple 1303 is used to measure the temperature of the target object and/or LITT probe. Because it is close to the tissue and probe, the temperature measurement results are more accurate than the remote temperature measurement of MRTI nuclear magnetic thermal imaging.
  • Figure 14 is a schematic diagram of temperature measurement using an FBG sensor according to some embodiments of this specification.
  • the temperature measurement element (temperature measurement element 611 or 661), such as the FBG sensor 1404-1, can be disposed in the integrated probe (LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660) , to measure the temperature of the LITT probe and/or target object.
  • the integrated probe LITT lateral ablation integrated probe 610 or LITT circumferential ablation integrated probe 660
  • the system When actually applied to temperature measurement, the system includes a terminal 1401, an ASE laser 1402, a circulator 1403, an FBG sensor 1404-1, a telecommunications spectrum analyzer 1405, and a temperature controller 1406.
  • the terminal 1401 may be, for example, a computer.
  • the ASE Laser 1402 has ultra wide bandwidth.
  • the ASE laser 1402 may be a three-in-one S, C and L band, 140nm ultra-wideband, 1530nm central wavelength ASE laser.
  • Circulator 1403 may be an ultra-bandwidth multimode high power circulator.
  • Telecommunications spectrum analyzer 1405 is a telecommunications spectrum analyzer with an analysis range of 600-1700nm.
  • Multiphysics software performs numerical calculations to predict the spatial distribution of intracranial interstitial tissue temperature and the degree of thermal degeneration set by the physician during LITT.
  • the geometry used for the simulation uses the LITT circumferential ablation probe 900 of the present invention (as shown in the figure).
  • the distal end of the LITT circumferential ablation probe 900 is sleeved with the distal glass through the main body 910 PEEK or polycarbonate PC tube.
  • ⁇ (kg/m 3 ) tissue density
  • c (J/kg ⁇ K) tissue specific heat
  • K (W/m ⁇ K) tissue thermal conductivity
  • T (°C) tissue temperature. Due to the use of in vitro model development, the effects of blood perfusion and metabolic heat production are actually 0;
  • Qi (W/m 3 ) is the laser-induced heat source.
  • preliminary angular measurements confirmed that the laser intensity is delivered in two directions: the radial emitted power of the diffusion part P1 (89% of the incident laser power in W) and the forward emitted power of the fiber tip P2 (89% of the incident laser power in W). 11%), based on these settings, the thermal response of the tissue during LITT irradiation is quantified as:
  • ⁇ 0 (cm -1 ) is the absorption coefficient of the tissue
  • ⁇ s (cm -1 ) is the scattering coefficient of the tissue
  • r (m) is the radial distance from the diffuser surface
  • l (m) is the diffuser length .
  • ⁇ ( ⁇ m) is the spot size of the laser beam and z (m) is the axial depth in the tissue.
  • the heat source is converted and quantified as:
  • the initial temperature of the entire tissue is set to 20°C, and the outer surface of the tissue is insulated (i.e. in is the direction of heat flow).
  • the Arrhenius parameter is used to determine the degree of thermal damage, mainly due to the temperature dependence of molecular reaction rates.
  • Table 1 shows the main parameter constant types for the optical properties of the target organ at 980 nm or 1064 nm, which are assumed to be constant during LITT treatment):
  • ⁇ S is affected by the temperature change of thermal expansion or contraction of the grating period and the thermo-optical effect (thermal-induced change of n eff ), which makes FBG can be used as a temperature sensing element.
  • the FBG sensor 1404-1 is obtained by combining the preparation process of FBG with the aforementioned raw materials, which allows the refractive index of the optical fiber core to be periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other. In turn, the input beam only experiences strong reflections at specific wavelengths determined by certain phase matching conditions. The reflected wavelength is called the Bragg wavelength ( ⁇ S ) of the FBG, and the phase matching condition is called the Bragg condition.
  • the quantification of ⁇ S is:
  • ⁇ T T H - T 0 , T 0 and TH are the reference and high temperatures applied to the FBG, respectively.
  • ⁇ S0 is the Bragg wavelength of FBG at T 0
  • ⁇ ⁇ and ⁇ n are the thermal expansion and thermo-optical coefficients of the monopole fiber produced as FBG, respectively.
  • the Bragg wavelength drift ⁇ S induced by the temperature change ⁇ T is quantified as:
  • the thermal sensitivity S of the FBG is quantified as:
  • the FBG sensor 1404-1 can monitor the interstitial tissue temperature during LITT laser irradiation in real time.
  • This calibration requires the temperature range under the control of the temperature controller 1406 in the FBG temperature measurement calibration mode (for example, -50°C to 180°C, -40°C to 150°C, -30°C to 120°C, -20°C to 100°C °C, etc.), perform this static calibration.
  • the system includes terminal 1401, ASE laser 1402, circulator 1403, FBG sensor 1404-2, telecommunications spectrum analyzer 1405, and temperature controller 1406.
  • the FBG sensor 1404-2 is placed in the temperature controller 1406 that can control the temperature between -40°C and 150°C.
  • the ASE laser 1402 may be an ultra-wideband ASE laser, and its broadband light reaches the FBG sensor 1404-2 through the circulator 1403.
  • the reflection signal of the FBG sensor 1404-2 enters the telecommunications spectrum analyzer 1405 through the circulator 1403, and the telecommunications spectrum analyzer 1405 is used to monitor the reflection spectrum of the FBG sensor 1404-2.
  • the calibration test is performed within a specific temperature range (for example, 10°C-80°C, 20°C-100°C, 30°C-120°C), with each temperature interval being 10°C and lasting 5 hours.
  • Figure 15 is an exemplary OCT probe according to some embodiments of the present specification.
  • the OCT probe 1500 has a long working distance and is suitable for assisting LITT in ablating large-sized target objects (for example, cancerous tissue).
  • the OCT probe 1500 includes an input port 1501, a first lens 1502, a second lens 1504, a beam deflection unit 1506, a spring torsion coil 1508, an optical sleeve 1510 and a filling body 1512.
  • the two end surfaces of the second lens 1504 are respectively welded to the first lens 1502 and the beam deflection unit 1506 through high-temperature fusion of specific materials, such as tungsten and iridium, and are fire polished to form a welded surface, so that the second lens 1504 is connected to the first lens 1504 .
  • the lens 1502 and the beam deflection unit 1506 are fixedly connected.
  • the light beam emitted by the light source of the OCT equipment enters the OCT probe 1500 through a specific optical path, such as the optical fiber slip ring device 212 and the input port 1501 (eg, single-mode optical fiber).
  • the input port 1501 is configured to input the light beam emitted by the light source to the OCT probe 1500 .
  • the light beam entering the OCT probe 1500 passes through the first lens 1502 and the second lens 1504 in sequence, and is deflected by the light beam deflection unit 1506 and exits the OCT probe 1500 .
  • the light beam emerging from the OCT probe 1500 may be used to illuminate the target object.
  • the first lens 1502 is configured to expand the light beam incident on the OCT probe 1500 (first lens 1502).
  • the incident light beam is a parallel light beam
  • the first lens 1502 can expand the parallel light beam.
  • the expanded beam has a certain divergence angle (also called beam expansion angle).
  • the first lens 1502 is cylindrical.
  • first lens 1502 is a coreless lens.
  • the beam expansion angle of the coreless lens is 2 ⁇ , where ⁇ is, for example, 5°, 10°, 15°, 20°, 25°, etc.
  • the coreless lens has a certain length b.
  • the focal length and focal spot size of the OCT probe 1500 are related to the length b of the coreless lens.
  • the second lens 1504 is disposed at the rear stage (rear end) of the first lens 1502 , and the light beam emitted from the first lens 1502 enters the second lens 1504 .
  • the second lens 1504 is configured to focus the light beam exiting the first lens 1502 to generate an exit spectrum with a certain focal length.
  • the second lens 1504 can also achromatically disperse the light beam exiting the first lens.
  • the second lens 1504 may be a micro-plano-convex spherical cylindrical lens.
  • the micro-plano-convex spherical cylindrical lens has a starting end and an end along the lens axis (for example, the direction of light beam propagation in the figure).
  • the starting end here is the end surface where the light beam is incident, and the end is the end surface where the light beam is emitted.
  • the starting end of the micro-plano-convex spherical cylindrical lens is a flat surface and the end is a convex spherical surface.
  • the part between the beginning and the end is a cylinder.
  • the cylinder has a certain cylinder diameter (ie, the cross-sectional diameter of the cylinder).
  • the cylinder diameter is, for example, 500 ⁇ m, 520 ⁇ m, 540 ⁇ m, 560 ⁇ m, 580 ⁇ m, 600 ⁇ m, 620 ⁇ m, etc.
  • the diameter of the cylinder is 560 ⁇ m, which can ensure that the light beam passes completely. Anything greater than or less than 560 ⁇ m will compromise the optical path performance (for example, less than 560 ⁇ m will cause the diffused optical path to be unable to be fully mechanically compatible with the OCT probe 1500, resulting in serious insertion loss and loss of imaging bandwidth).
  • the optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is, for example, -1.5mm, -1.6mm, -1.7mm, -1.8mm, -1.9mm, -2mm, -2.1mm, etc.
  • the optical curvature r of the terminal convex spherical surface of the micro plano-convex spherical cylindrical lens is -1.8 mm.
  • the -1.8mm curvature is the key to ensuring that the OCT probe 1500 exceeds the effective working distance of 1cm. Otherwise, the focal length will shift inward to reduce the working distance, expand the spot, reduce lateral resolution, and reduce imaging quality.
  • the materials used in the micro plano-convex spherical cylindrical lens are, for example, N-LAF3, SF11, N-SF11 and other optical materials.
  • the material used in the micro plano-convex spherical cylindrical lens is N-LAF3.
  • the micro-plano-convex spherical cylindrical lens has a certain refractive index n.
  • the refractive index n is, for example, 1.3, 1.4, 1.5, 1.6, 1.7, 1.8, etc.
  • the starting end of the second lens 1504 (ie, the beam incident end surface) is a polished surface and has a certain angle.
  • the angle here is the angle between the vertical plane of the axis of the second lens 1504 and the starting end surface of the second lens 1504 .
  • the angles are, for example, 0°, 2°, 4°, 6°, 8°, 10°, etc. In some embodiments, the angle is 0° or 8°. When the angle is 0°, the mechanical stress performance can be increased after fire polishing of the welding surface; when the angle is 8°, the TIR pollution value of the lens welding surface can be significantly reduced and the insertion loss is reduced.
  • the beam deflection unit 1506 is disposed at the rear stage (rear end) of the second lens, and the beam exiting the second lens 1504 enters the beam deflection unit 1506 .
  • the beam deflection unit 1506 is configured to deflect the light beam that exits the second lens 1504 , and the deflected light beam exits the OCT probe 1500 .
  • the beam deflection unit 1506 includes a cylindrical core and a hard cladding located around the core.
  • the beam deflection unit 1506 includes a beveled end surface, and the beveled end surface is coated with a metal plating layer.
  • the beam deflection unit 1506 may be similar to the LITT lateral ablation probe 700 described in FIG. 7 .
  • the beam deflection unit 1506 includes a main body, a connection surface and a coating.
  • the main body includes a fiber core and a hard cladding located on the periphery of the fiber core.
  • the core is made of pure silica material.
  • the hard cladding is made of Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • the end face of the main body has a certain inclination angle, which is the beveled end face. At this time, the end face of the main body forms a certain angle with the axis of the main body.
  • the included angle is 0-90°, and does not include this range. endpoint.
  • the connection surface is the connection interface between the chamfered end surface and the plating layer.
  • the connecting surface is formed by smoothing the chamfered end surface.
  • the connection surface is coated with the plating layer (for example, a noble metal plating layer).
  • the precious metals may include, for example, gold, silver, and platinum group metals.
  • the coating can be formed on the surface of the connection surface by, for example, magnetron sputtering coating.
  • the angle between the coating and the axis of the body is, for example, 35°, 37°, 39°, 41°, 43°, 45°, 47°, 49°, etc.
  • the truncated axial cylinder of the beam deflection unit 1506 has a certain length.
  • the truncated axial cylinder is the cylinder between the beam incident end surface of the beam deflection unit 1506 and the bevel point of the beveled end surface.
  • the bevel point is the point on the bevel end surface that is closest to the beam incident end surface of the beam deflection unit 1506 .
  • the cut-off axial cylinder length is, for example, 2 ⁇ m, 5 ⁇ m, 8 ⁇ m, 10 ⁇ m, etc. In some embodiments, the length of the truncated axial cylinder is 5 ⁇ m, in which case the spectral deflection effect of the beam deflection unit 1506 is better.
  • the spring torsion coil 1508 is disposed at the front end of the OCT probe 1500 .
  • one end of the spring torsion coil 1508 is in contact with the starting end of the second lens 1504 .
  • the spring torsion coil 1508 provides rotational torsion support for the OCT probe 1500 through its properties of lifting, compressing and twisting.
  • optical sleeve 1510 is used to accommodate the spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506.
  • optical tube 1510 is a tubular optical element, such as tubular optical glass.
  • the spring torsion coil 1508, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 are arranged in the optical tube 1510 in sequence.
  • the optical sleeve 1510 has light transmittance. The light beam emitted through the beam deflection unit 1506 passes through the optical sleeve 1510 and exits the OCT probe 1500.
  • the filling body 1512 is filled inside the optical sleeve 1510 .
  • the filling body 1512 is optical glue, which solidifies after a certain period of time after filling.
  • the filling body 1512 can be filled between the first lens 1502 , the second lens 1504 , the beam deflection unit 1506 and the optical sleeve 1510 In the gap, the first lens 1502, the second lens 1504 and the beam deflection unit 1506 can be fixed relative to the optical tube 1510.
  • the refractive index of the filling body 1512 is much smaller than the refractive index of the second lens (for example, the micro-plano-convex spherical cylindrical lens) to avoid affecting the propagation of the light beam in the OCT probe 1500 Make an impact.
  • the second lens for example, the micro-plano-convex spherical cylindrical lens
  • the ABCD optical Gaussian transmission matrix T of the OCT probe 1500 can be expressed as:
  • the Gaussian transmission moment M at any length z of the OCT probe 1500 emission spectrum can be expressed as the formula:
  • the central wave number of the light source is defined as k 0
  • the wavelength under different traversals i in the spectral bandwidth range is ⁇
  • the probe focal length under different b values is:
  • the focus spot radius under different b values is:
  • the focal length and focus spot size of the OCT probe 1500 can be adjusted, thereby changing the working distance of the OCT probe 1500 to make it Can be applied to pathological imaging of large-sized tissues.
  • Figure 16 is a schematic diagram of preparing an FBG sensor according to some embodiments of this specification.
  • the FBG sensor is obtained by irradiating specially prepared raw materials through FBG irradiation equipment 1600 .
  • the specially prepared raw materials must meet specific parameter conditions.
  • the parameter conditions are as mentioned above and will not be repeated here.
  • the FBG irradiation equipment 1600 includes a terminal 1601, a laser controller 1602, a laser 1603, beam correction devices 1604-1 and 1604-2, a slit diaphragm 1605, a UV coating lens 1606, a phase mask 1607, and a slide rail 1609. Fixation device 1610, motion driver 1611, and motion drive controller 1612.
  • the terminal 1601 connects and controls the laser controller 1602 and the motion drive controller 1612.
  • Terminal 1601 may be, for example, a computer.
  • the laser controller 1602 connects and controls the laser 1603 to emit laser light.
  • Laser 1603 may be an excimer pulsed laser with a specific characteristic wavelength (eg, 248 nm).
  • the power of the laser it generates can be, for example, 8W, 10W, 12W, 15W, etc.; its pulse frequency can be, for example, 90Hz, 100Hz, 120Hz, etc.; its pulse energy can be, for example, 100mJ, 120mJ, 140mJ etc.
  • the laser generated by the laser 1603 is a flat-top laser beam with almost uniform flux (energy density).
  • the spot emission of the laser beam is characterized by a rectangular flat-top, and its central wavelength is, for example, 248 nm; its pulse duration is , for example, 10ns, 12ns, 15ns, 20ns, etc.; the rectangular flat top is, for example, 4 ⁇ 1mm 2 , 6 ⁇ 1.5mm 2 , 10 ⁇ 3mm 2 , etc.; its divergence angle is, for example, 2 ⁇ 1mrad 2 , 3 ⁇ 2mrad 2 , 4 ⁇ 2mrad 2 , etc.
  • the beam correction devices 1604-1 and 1604-2 are used to deflect the beam and correct the optical path.
  • the beam correction devices 1604-1 and 1604-2 are both 248 nm characteristic wavelength excimer laser 45° line mirrors, used to deflect the laser light generated by the laser 1603 at 45° and perform optical path correction.
  • the slit diaphragm 1605 is used to limit the propagation of light beams in specific directions.
  • the size of the slit aperture 1605 ie, the width of the slit
  • the size of slit aperture 1605 is, for example, 2-6 mm. In some embodiments, the size of slit aperture 1605 is 2 mm. In some embodiments, slit aperture 1605 measures 3 mm. In some embodiments, slit aperture 1605 measures 4.5 mm. In some embodiments, slit aperture 1605 measures 6 mm. In this embodiment, the slit diaphragm 1605 is a mechanical slit device with an adjustable width of 4.5 mm.
  • the ultraviolet coated lens 1606 is used to focus the laser beam in the ultraviolet region.
  • the UV-coated lens 1606 may be a UV-coated fused silica plano-convex cylindrical lens.
  • the UV-coated fused silica plano-convex cylindrical lens can focus the light beam (focal length is, for example, 150mm, 200mm, 250mm, etc.) to the phase mask 1607.
  • the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 100-600nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 200-500 nm. In some embodiments, the characteristic wavelength of the UV-coated fused silica plano-convex cylindrical lens is 245-440 nm.
  • the phase mask 1607 is disposed in front of the raw material 1608. After being irradiated with a laser beam, strip-shaped spots can be formed on the raw material 1608.
  • the phase mask 1607 is an ultraviolet irradiation 248nm characteristic wavelength ultra-bandwidth (for example, 1460-1600nm) phase mask.
  • the width of the strip-shaped light spot is, for example, 10 mm, 15 mm, 20 mm, 25 mm, etc.; the height is, for example, 28 ⁇ m, 32.4 ⁇ m, 40 ⁇ m, 50 ⁇ m, etc.
  • the motion drive controller 1612 is connected to and controls the motion driver 1611 to drive the fixation device 1610 to move, for example, translation and/or rotation.
  • the specially prepared raw materials are irradiated by the FBG irradiation equipment 1600.
  • the process of preparing the FBG sensor includes the following steps:
  • S16-1 Fix both ends of the raw material 1608 to the slide rail 1609 and the fixing device 1610 respectively.
  • the fixing device 1610 is fixedly connected to the motion driver 1611.
  • Fixing device 1610 may be a clamp.
  • the clamp may clamp and secure one end of the raw material 1608 .
  • the laser controller 1602 controls the laser 1603 to emit laser. After the laser passes through the above-mentioned beam correction devices 1604-1 and 1604-2, the slit diaphragm 1605, the ultraviolet coating lens 1606 and the phase mask 1607, Strip-shaped light spots are generated on the surface of the raw material 1608.
  • the motion drive controller 1612 controls the motion driver 1611 to drive the raw material 1608 to move. During the movement of the raw material 1608, the laser irradiates the raw material 1608 to form the FBG sensor.
  • the fixing device 1610 is fixedly connected to the motion driver 1611.
  • the motion drive controller 1612 controls the motion driver 1611 to drive the fixing device 1610 to move
  • the raw material 1608 also moves (translation, rotation, etc.) accordingly.
  • the strip-shaped spot formed by the laser through the phase mask 1607 is irradiated on the surface of the raw material 1608, so that the refractive index of the optical fiber core is periodically modulated.
  • Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at a specific wavelength determined by a certain phase matching condition, called the Bragg wavelength of the FBG, which ultimately forms the FBG sensor.
  • Figure 17 is a schematic diagram of a medical treatment device according to some embodiments of the present specification.
  • the medical treatment device 1700 may be a device that integrates various devices and components in the medical treatment system 100 (local or remote). As shown in the figure, the medical treatment device 1700 may include MRI equipment (not shown in the figure), LITT equipment (not shown in the figure), temperature measurement equipment (not shown in the figure), OCT equipment (not shown in the figure) ), control device 1710, interface platform line control module 1720, driving component 1730, probe group 1740, temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser Power Attenuator 1790.
  • MRI equipment not shown in the figure
  • LITT equipment not shown in the figure
  • temperature measurement equipment not shown in the figure
  • OCT equipment not shown in the figure
  • the MRI equipment is used to image a specific area including a target object (for example, a cancer lesion) to generate an MRI image.
  • the MRI image may be a real-time MRI image or a non-real-time MRI image.
  • the MRI image may include a three-dimensional image or multiple two-dimensional images (eg, cross-sectional, coronal, and sagittal images), representing information (eg, position and size, etc.) of the target object in the three-dimensional space.
  • the information about the target object in the three-dimensional space provided by the MRI image can be used before treatment.
  • the LITT probe, the OCT probe and/or the temperature measurement element of the temperature measurement device of the probe set 1740 pass through the human tissue to reach the target.
  • the path at the object is planned (referred to as needle entry planning).
  • the information of the target object in the three-dimensional space provided by the MRI image can also be used in the treatment process to guide the LITT probe, OCT probe and/or temperature measurement element to enter the human tissue according to the planned path and reach the Target object (referred to as needle insertion guide).
  • the MRI image may be displayed on a terminal (eg, terminal 150).
  • a user such as a doctor, can perform needle insertion planning and needle insertion guidance of the LITT probe and/or temperature measurement element based on the MRI image through a terminal (for example, a touch screen, a mouse, a keyboard and other physical components on the terminal 150).
  • the system can also automatically perform needle insertion planning and needle insertion guidance for the LITT probe and/or temperature measurement element based on the MRI image.
  • the MRI equipment can also perform magnetic resonance thermography on a specific area including the target object to generate a thermal image.
  • the thermal image may be registered with the MRI image to simultaneously represent the anatomical structure information of the specific region containing the target object and the temperature change information of the corresponding location.
  • the LITT equipment is used to generate laser light and use the thermal effect of the laser to treat the target object.
  • the LITT device includes a laser, a LITT probe (eg, a LITT lateral ablation probe, a LITT circumferential ablation probe), and a channel (such as an optical fiber) and interface connecting the laser and the LITT probe.
  • the laser may include a tunable laser diode and/or a non-tunable laser diode.
  • the laser power of the tunable laser diode is tunable within a specific range, such as 0-500W, 0-250W, 0-50W, 0-10W, 1-8W, etc.
  • the laser power of the non-tunable laser diode is a specific value, for example, 1W, 3W, 5W, 8W, 10W, 12W, 15W, 20W, 30W, 60W, 100W, etc.
  • the laser has certain characteristic wavelengths, such as 840nm, 980nm, 1064nm, 1300nm, etc.
  • the temperature measuring device includes a temperature measuring element.
  • the temperature measurement element is used to measure the temperature of the target object or a specific position on its edge (for example, the position on the edge of the target object farthest from the LITT probe) to determine the temperature within the entire target object range. Tissue temperature to ensure treatment effect.
  • the distance between the LITT probe and the temperature measuring element is smaller than the size of the target object.
  • the edges of the target object are irregularly shaped.
  • the target object may be equivalent to a circle.
  • the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object.
  • the size of the target object is, for example, the diameter of the equivalent circle.
  • Temperature measurement elements can include thermocouples (such as K-type thermocouples), LITT photon temperature measurement probes, etc.
  • the temperature measurement element may be a LITT photon temperature measurement probe.
  • the LITT photon temperature measurement probe may include an FBG temperature measurement probe.
  • the FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.), causing the fiber core to refract The rate is periodically modulated. Periodic core index modulation produces core patterns that are reflected or transmitted through numerous index boundaries and interfere with each other.
  • the input beam only experiences strong reflection at a specific wavelength determined by certain phase matching conditions.
  • the reflected wavelength is called the Bragg wavelength of the FBG.
  • the phase matching condition called the Bragg condition, ultimately forms the FBG temperature measurement probe.
  • the FBG thermometric probe can be used for real-time monitoring of interstitial tissue at specific locations during laser ablation irradiation.
  • the OCT device Based on the light transmittance of biological structures, the OCT device detects the reflection, scattering and other signals of biological tissues, converts them into electrical signals, and generates OCT images.
  • the OCT image is a real-time OCT image, or a non-real-time OCT image.
  • the OCT device includes a light source, an OCT probe, an interference component, and an optical fiber and an interface connecting the components.
  • the light source uses a low-coherence light source to improve the longitudinal resolution of the imaging.
  • the OCT device can be a dual-mode OCT, and its light source can generate optical signals with two different parameters (bandwidth, central wavelength).
  • the dual-mode OCT uses an optical signal with a bandwidth of more than 160nm and a central wavelength of 840nm, and a sweep range of more than 100nm and a central wavelength of 1300nm.
  • Dual-mode OCT can provide pathological imaging with a resolution close to 1 ⁇ m and a depth of cm, so as to perform real-time pathological imaging of the actual morphology of ablation pathology and cell apoptosis, and then perform pathological evaluation.
  • the probe set 1740 includes the LITT photon ablation probe 1742 of the LITT device and the LITT photon thermometry probe 1744 of the temperature measurement device.
  • the above-mentioned LITT probe for example, LITT lateral ablation probe, LITT circumferential ablation probe
  • OCT probe can be integrated into one body to form an integrated probe integrating diagnosis and treatment (hereinafter referred to as integrated probe for short). probe).
  • LITT photon ablation probe 1742 may be the integrated probe.
  • the LITT photon temperature measurement probe 1744 and the LITT photon ablation probe 1742 are independent of each other (eg, have independent structures and are independently controlled).
  • the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 of the temperature measurement device are arranged at different positions relative to the target object.
  • the control device 1710 can be used to control one or more devices or components of the medical treatment device 1700 and perform corresponding operations.
  • the control device 1710 can generate corresponding instructions based on the device or component being controlled and the operations that need to be performed.
  • the instructions are conveyed to the corresponding device or component in the form of electrical signals, causing the device or component to perform corresponding operations.
  • the control device 1710 may include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip ( SoC) etc.
  • the control device 1710 may be an industrial computer.
  • the control device 1710 integrates an OCT control module 1711, a LITT control module 1713, an FBG control module 1715, a probe sensing module 1717, and a drive control module 1719.
  • the OCT control module 1711 is used to control OCT imaging of the target object.
  • the OCT control module 1711 can generate instructions to control the OCT device to emit and receive optical signals and/or set imaging parameters (eg, optical signal bandwidth, central wavelength of the optical signal, imaging time, image contrast, etc.).
  • the OCT control module 1711 can control the OCT device to emit a dual-mode OCT optical signal with a central wavelength of 840 nm exceeding a bandwidth of 160 nm, and a central wavelength of 1300 nm exceeding a 100 nm sweep range.
  • the optical signal is transmitted to the optical fiber slip ring device 1722, and after motion control and spatial coupling processing is performed on the optical fiber slip ring device 1722, it is finally transmitted to the OCT probe.
  • the OCT control module 1711 may also acquire the generated pathological diagnosis signal (eg, an optical signal carrying tissue pathological characteristics) to generate an OCT image.
  • the generated pathological diagnosis signal eg, an optical signal carrying tissue pathological characteristics
  • the LITT control module 1713 can control the LITT photon ablation probe 1742 to perform ablation treatment on the target object.
  • LITT control module 1713 integrates a laser controller.
  • the laser controller can control the laser of the LITT device (eg, the tunable laser diode and/or the non-tunable laser diode) to emit laser light to provide an ablation energy source for the entire LITT.
  • the LITT control module 1713 can control the laser to emit laser, and the emitted laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724.
  • the LITT control module 1713 controls the laser of the LITT device to emit laser light of a specific wavelength (e.g., 980 nm or 1064 nm) with a specific power (e.g., at a power selected in the range of 1-8W), and the laser is transmitted to the optical path relay processing
  • the device 1724 performs a physical connection of the light path relay, and then transmits it to the LITT photon ablation probe 1742, which emits an ablation laser to ablate the target tumor tissue.
  • the FBG control module 1715 can control the temperature measuring element to obtain the temperature of a specific position on the edge of the target object.
  • the temperature measurement signal of the temperature measurement element (such as the heat source optical signal of the LITT photon temperature measurement probe 1744) can be transmitted through the optical path relay processing device 1724.
  • the FBG control module 1715 can control the LITT photon temperature probe 1744 to detect in real time a specific position on the edge of the target object (for example, the farthest edge of the tumor tissue, the farthest edge is ablated with LITT photons).
  • the probe 1742 is the temperature of the geometric distance measuring point, and transmits the temperature to the optical path relay processing device 1724, and finally to the FBG control module 1715.
  • the optical path relay processing device 1724 supports and ensures the optical path ring output to avoid conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path.
  • the FBG control module 1715 can modulate the spectral signal carrying the temperature scale benchmark, and convert the spectral signal into a specific temperature in the form of an electrical signal.
  • the probe sensing module 1717 can detect the real-time position of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 in real time by controlling the displacement controller 1726.
  • the probe sensing module 1717 may trigger changes in position signal feedback across the ergodic displacement controller 1726 by emitting an electrical signal, and the displacement controller 1726 may monitor and communicate with the dual-axis three-dimensional frame 1736 and the single-axis stereoscopic frame 1736 in real time, for example, through a displacement sensor.
  • the axis three-dimensional frame 1738 interacts to obtain the position information of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 in a specific part of the patient (for example, within the skull or other organs of the human body) in real time.
  • the probe sensing module 1717 can also send control signals to the displacement controller 1726 in real time, issue displacement triggering instructions and receive position feedback processing signals.
  • the displacement triggering instruction is used to trigger the displacement controller 1726 to control the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744.
  • the position feedback processing signal is used to determine and decide on the subsequent positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744 based on the real-time positions of the LITT photon ablation probe 1742 and/or the LITT photon temperature probe 1744. Movement (e.g., moving forward, adjusting direction, retracing, etc.).
  • At least one displacement sensor is mounted on the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively. At least one displacement sensor on the biaxial three-dimensional frame 1736 is used to monitor the movement of the LITT photon ablation probe 1742. At least one displacement sensor on the uniaxial three-dimensional frame 1738 is used to monitor the movement of the LITT photon temperature probe 1744.
  • the displacement sensor may be, for example, a piezoelectric sensor, an inductive sensor, an eddy current sensor, etc.
  • the drive control module 1719 can send instructions through electrical signals to control the first drive device 1732 and/or the second drive device 1734 in the drive assembly 1730 to drive the movement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744.
  • the first driving device 1732 also known as the ablation end driving device, is connected to and drives the LITT photon ablation probe 1742 to move (for example, translational, rotational motion) to achieve precise motion control of the LITT photon ablation probe 1742 with two degrees of freedom.
  • the second driving device 1734 is also called the temperature measurement end driving device, which is connected to and drives the movement (for example, translational movement) of the LITT photon temperature measurement probe 1744 to realize precise motion control of the LITT photon temperature measurement probe 1744 with one degree of freedom.
  • the movement of the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 requires mechanical clamping and power transmission support provided by the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 respectively.
  • the biaxial three-dimensional frame 1738 provides two different Power transmission with a single degree of freedom.
  • a single axis provides power transmission with a single degree of freedom.
  • the interface platform hub control module 1720 integrates mid-level or relay control of one or more components or elements of the medical treatment device 1700 .
  • the interface platform line control module 1720 integrates the above-mentioned optical fiber slip ring device 1722, optical path relay processing device 1724 and displacement controller 1726.
  • the interface platform hub control module 1720 includes a packaging box.
  • the optical fiber slip ring device 1722, the optical path relay processing device 1724, and the displacement controller 1726 are provided in the packaging box and connected to corresponding components or components through respective corresponding channels.
  • the optical fiber slip ring device 1722 is connected to the OCT probe through the OCT probe channel (optical fiber); the optical path relay processing device 1724 is connected to the LITT probe and the LITT photon measurement probe through the LITT ablation probe channel and the LITT temperature measurement probe channel respectively. Temperature probe 1744; displacement controller 1726 is connected to the displacement sensor through a displacement sensor cable channel.
  • the optical fiber slip ring device 1722 may be disposed on the propagation path of the optical signal generated by the OCT device (for example, at the rotary joint).
  • the optical fiber slip ring device is used to ensure uninterrupted transmission of optical signals.
  • a multi-channel optical fiber slip ring device can be used (such as a dual-channel optical fiber slip ring device to adapt to the above-mentioned two optical signals with different central wavelengths), also called a multi-mode optical fiber slip ring device.
  • the optical path relay processing device 1724 is used to process optical signals and ensure the continuity of optical signal propagation.
  • the laser light emitted by the laser of the LITT device is processed by the optical path relay processing device 1724 and then transmitted to the LITT probe.
  • the optical path relay processing device 1724 can adjust at least one parameter (eg, power, frequency, etc.) of the laser.
  • the optical path relay processing device 1724 can compensate for the attenuation of the laser so that it reaches a specific power, or perform attenuation processing on the laser so that its power meets the needs of treatment.
  • the optical path relay processing device 1724 supports and ensures the opposite transmission of the optical paths of the temperature measurement equipment to avoid the conflict between the temperature measurement output optical path carrying temperature information and the temperature measurement incident optical path, thereby interrupting or interfering with each other in optical signals.
  • the displacement controller 1726 may control the displacement of the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 based on instructions from the probe sensing module 1717 .
  • the displacement controller 1726 can control the LITT photon ablation probe 1742 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT ablation probe channel provided on the biaxial stereoscopic frame 1736 ), according to the needle insertion planning and needle insertion guidance of the LITT photon ablation probe 1742, the location of the target object is reached.
  • the displacement controller 1726 can control the LITT photon temperature measurement probe 1744 to pass through a specific part of the patient (for example, through the skull and into the skull) through the LITT temperature measurement probe channel fixedly provided on the single-axis three-dimensional frame 1738.
  • the needle insertion plan and needle insertion guide of the LITT photon temperature measurement probe 1744 the location of the target object is reached to measure the temperature of the edge of the target object or surrounding tissue located at a specific distance from the LITT photon temperature measurement probe 1744.
  • the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 are fixed to similar positions on specific parts of the patient (eg, head, chest, limbs, etc.).
  • the driving component 1730 is used to drive the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move, so that the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 reaches or moves away from a specific position (for example, , the location of the target object).
  • the movement of the LITT photon ablation probe 1742 may include translational movement and rotational movement.
  • the movement of the LITT photon thermometer probe 1744 may include translational movement.
  • the driving assembly 1730 includes a first driving device 1732 (also called an ablation end driving device) and a second driving device 1734 (also called a temperature measurement end driving device), which respectively control the LITT photon ablation probe 1742 and The LITT photon thermometer probe 1744 moves.
  • the first driving device 1732 is independent of the second driving device 1734 .
  • Each drive device may include a drive motor, cables, and motion control mechanisms.
  • the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 are physically connected to corresponding motion control mechanisms through respective connected cables. Through corresponding cables and motion control mechanisms, the force output by the corresponding drive motor can be transmitted to the LITT photon ablation probe 1742 and the LITT photon temperature measurement probe 1744 to control their movement.
  • the first driving device 1732 is coupled to the LITT photon ablation probe 1742 and controls the translational movement and rotational movement of the LITT photon ablation probe 1742.
  • the first driving device 234 includes a first driving motor, a first translation cable, a first translation control mechanism, a first rotation cable, and a first rotation control mechanism.
  • the first translation control mechanism is used to control the translation movement of the LITT photon ablation probe 1742.
  • the first rotation control mechanism is used to control the rotation movement of the LITT photon ablation probe 1742.
  • the first translation cable and the first rotation cable are respectively connected to the first translation control mechanism and the first rotation control mechanism, and the first translation control mechanism and the first rotation control mechanism are connected to the LITT photon ablation
  • the probe 1742 controls the translational movement and rotational movement of the LITT photon ablation probe 1742 through the first translation cable and the first rotation cable respectively.
  • the first drive motor can drive the movement of the first translation cable and/or the first rotation cable as required, thereby controlling the translation and/or rotation movement of the LITT photon ablation probe 1742 to achieve the LITT photon ablation. Precise motion control of probe 1742 with two degrees of freedom.
  • the first translation control mechanism and the first rotation control mechanism may be provided on the biaxial three-dimensional frame 1736 .
  • the second driving device 1734 is coupled to the LITT photon temperature measurement probe 1744 and controls the translational movement of the LITT photon temperature measurement probe 1744.
  • the second driving device 1734 includes a second driving motor, a second translation cable, and a second translation control mechanism.
  • the second translation control mechanism is used to control the translation movement of the LITT photon temperature measurement probe 1744.
  • the second translation cable is connected to the second translation control mechanism, the second translation control mechanism is connected to the LITT photon temperature measurement probe 1744, and the LITT photon temperature measurement probe is controlled through the second translation cable. Translational movement of temperature probe 1744.
  • the second drive motor can drive the movement of the second translation cable as required, thereby controlling the translational movement of the LITT photon temperature measurement probe 1744 and achieving precise motion control of one degree of freedom of the LITT photon temperature measurement probe 1744 .
  • the second translation control mechanism may be provided on the single-axis three-dimensional frame 1738.
  • the above-mentioned cables are special silk threads with higher rigidity and lower elastic modulus, and can complete torque transmission in real time 1:1 to ensure the accuracy of driving the LITT photon ablation probe 1742 and/or the LITT photon temperature measurement probe 1744 to move.
  • Biaxial stereoscopic frame 1736 and uniaxial stereoscopic frame 1738 may carry one or more components or elements of medical treatment device 1700 .
  • the components or elements carried by the biaxial three-dimensional frame 1736 include the LITT ablation probe channel of the LITT photon ablation probe 1742, a displacement sensor, a first motion control mechanism (such as the first translation control mechanism and the first Rotation control mechanism), etc.
  • the components or elements carried by the single-axis three-dimensional frame 1738 include the LITT temperature measurement probe channel of the LITT photon temperature measurement probe 1744, a displacement sensor, a second translation control mechanism, etc.
  • the biaxial three-dimensional frame 1736 and the single-axis three-dimensional frame 1738 can be fixed to a specific part of the patient (for example, two different positions of the skull), and maintain a stable connection with the specific part of the patient without relative displacement.
  • the components or elements carried by the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738 can be fixedly connected to the biaxial three-dimensional frame 1736 and the single-axial three-dimensional frame 1738, respectively.
  • the temperature feedback control unit 1750 is used to monitor the temperature at a specific position on the edge of the target object measured by the LITT photon temperature probe 1744, and ensure that the measured temperature is within a preset temperature range.
  • the preset temperature range is set by the user, based on system default settings, etc.
  • the preset temperature range is 44 ⁇ 0.5°C, 44 ⁇ 1°C, 45 ⁇ 0.5°C, 45 ⁇ 1°C, 46 ⁇ 0.5°C, 46 ⁇ 1°C, 47 ⁇ 0.5°C, 47 ⁇ 1°C, 48 ⁇ 0.5°C, 48 ⁇ 1°C, etc.
  • the preset temperature range is 46 ⁇ 1°C.
  • the target object's tissue temperature is within this preset temperature range for better therapeutic effects.
  • the temperature feedback control unit 1750 is connected to the FBG control module 1715.
  • the FBG control module 1715 may transmit the temperature measured by the LITT photon temperature probe 1744 to the temperature feedback control unit 1750 as an electrical signal.
  • the transmission of the measured temperature may be real-time or intermittent (eg, periodic).
  • the temperature feedback control unit 1750 may determine the difference between the measured temperature and the preset temperature range (i.e. temperature difference), and output the difference value to the laser dose control unit 1760 to adjust the laser dose output by the LITT photon ablation probe 1742, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to the preset temperature within the range.
  • the laser dose control unit 1760 can determine the target laser output dose value (ie, the target laser dose value that needs to be output).
  • the laser dose control unit 1760 can be connected to the temperature feedback control unit 1750.
  • the laser dose control unit 1760 can obtain the value determined by the temperature feedback control unit 1750. temperature difference, and based on the temperature difference, the target laser output dose value is determined.
  • the target laser output dose value can be the total dose of laser within a specific time period, or it can be the dose value of laser at each time. Through the total dose of the laser during the time period or the dose value of the laser at each moment, the changing trend of the tissue temperature at the LITT photon temperature measurement probe 1744 can be determined, so that the temperature measured by the LITT photon temperature measurement probe 1744 returns to within the preset temperature range.
  • the above process of determining the changing trend of tissue temperature at the LITT photon thermometer probe 1744 can be determined based on a model or a specific algorithm.
  • the model may be, for example, a machine learning model.
  • Exemplary machine learning models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support vectors Machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosted decision tree (GBDT) model, LambdaMART model, adaptive enhancement model, hidden Martian Kov model, perceptron neural network model, Hopfield network model, etc.
  • neural network models e.g., deep learning models
  • GAN generative adversarial networks
  • DBN deep belief networks
  • SAE stacked autoencoders
  • LR logistic regression
  • SVM support vectors Machine
  • decision tree model
  • Exemplary deep learning models may include deep neural network (DNN) models, convolutional neural network (CNN) models, recurrent neural network (RNN) models, feature pyramid network (FPN) models, etc.
  • Exemplary CNN models may include V-Net models, U-Net models, FB-Net models, Link-Net models, etc., or any combination thereof.
  • the model can be trained through historical data (for example, historical laser dose and historical temperature difference), thereby generating a trained model to determine the target laser output dose value.
  • the attenuator adjustment control unit 1770 can be connected to and control the attenuator adjustment unit 1780 so that the laser power attenuator 1790 adjusts the power of the output laser.
  • laser power attenuator 1790 may be an SMA variable high power laser attenuator.
  • the SMA variable high-power laser attenuator is provided with a power adjustment nut. By adjusting the forward and reverse adjustment of the nut, the output laser power can be adjusted.
  • the attenuator adjustment control unit 1770 may determine the adjustment direction and adjustment amount of the adjustment nut (for example, the number of turns of the nut) based on the current laser output dose value and the target laser output dose value.
  • the temperature feedback control unit 1750, the laser dose control unit 1760 and/or the attenuator adjustment control unit 1770 can be integrated as a processing module, and the processing module operates independently with respect to the control device 1710 and is connected with the medical device 1710.
  • the various components or devices of treatment device 1700 are connected to each other.
  • the processing module may determine the target laser output dose value of the LITT device based on the difference between the measured temperature and the preset temperature range, so that the temperature measured by the temperature measuring element is within the preset temperature range.
  • the processing module may be or include, for example, a microcontroller (MCU), a central processing unit (CPU), a programmable logic device (PLD), an application specific integrated circuit (ASIC), a single chip microcomputer (SCM), a system on a chip (SoC) etc.
  • MCU microcontroller
  • CPU central processing unit
  • PLD programmable logic device
  • ASIC application specific integrated circuit
  • SCM single chip microcomputer
  • SoC system on a chip
  • the attenuator adjustment unit 1780 can be connected to and control the laser power attenuator 1790.
  • the attenuator adjustment unit 1780 can control the laser power attenuator 1790 to attenuate or gain the input laser power by a certain proportion based on the instructions generated by the attenuator adjustment control unit 1770 (for example, the adjustment direction and adjustment amount of the above-mentioned nut).
  • the laser power attenuator 1790 is an SMA variable high-power laser attenuator.
  • the attenuator adjustment unit 1780 can be, for example, an electric screw adjustment stepping element.
  • the electric screw adjustment stepping element can include a micro drive motor. Through the micro drive motor, the nut can be adjusted according to the determined adjustment direction and adjustment amount of the nut.
  • the laser power attenuator 1790 can adjust the current laser output dose value to the target laser output dose value by attenuating or gaining a certain proportion of the input laser power.
  • the laser power attenuator 1790 can attenuate the input laser power by, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80% or 90%, or gain, for example, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, 100%, 120%, 150%, etc. (i.e. power attenuation/gain processing).
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measuring element is always within the preset temperature range.
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measurement element measures The obtained temperature is always within the preset temperature range. At this time, the laser power output by the laser of the LITT device is always the target laser output dose value.
  • the laser is transmitted to the LITT photon ablation probe 1742 through the optical path relay processing device 1724 to reach Adjust and adapt the laser ablation energy to the purpose.
  • the operation between the above-mentioned modules, units or components can be a dynamic adjustment process, through a back-and-forth cycle, so that the temperature measured by the LITT photon temperature measurement probe 1744 (for example, the temperature of the farthest edge of the target object) is always dynamically maintained at within the preset temperature range. Electrical connections are established between each unit, and the temperature control signal is transmitted in real time and stably in the form of an electrical signal. Combined with the accuracy of the LITT photon temperature measurement probe 1744 (more accurate than the previous MRTI temperature measurement), the temperature is increased. The precision of the control and the timeliness of the feedback adjustment ensure that the temperature at the farthest edge of the target object relative to the LITT photon ablation probe 1742 is always maintained within the preset temperature range, thus ensuring the treatment effect.
  • Figure 18 is a schematic diagram of a LITT photon temperature measurement probe according to some embodiments of the present specification.
  • the LITT photon temperature measurement probe 1805 is arranged in a probe sleeve, which is made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK).
  • LITT photon temperature measurement probe 1805 can be an FBG temperature measurement probe (also known as FBG sensor).
  • the FBG temperature measurement probe includes an optical fiber prepared using special raw materials, which is irradiated with ultraviolet light in a specific wavelength range (for example, 240-244nm, 244-248nm, 248-252nm, 252-256nm, etc.).
  • the raw material for preparing the FBG temperature measurement probe can be fixed on a fixing device (for example, a clamp), and the fixing device is fixedly connected to the motion driver.
  • the laser controller controls the laser to emit laser, which passes through the beam correction device (for example, two oppositely arranged 248nm characteristic wavelength excimer laser 45° line mirrors), the slit diaphragm (for example, a 4.5mm width diaphragm) ), after UV coating lens (for example, 245-440nm characteristic wavelength UV coating fused silica plano-convex cylindrical lens) and phase mask (for example, UV irradiation 248nm characteristic wavelength 1460-1600nm ultra-bandwidth phase mask), after the raw material Strip-like spots appear on the surface.
  • the motion drive controller controls the motion driver to drive the raw material to move. During the movement of the raw material, the raw material is irradiated by the laser, thereby forming the FBG temperature measurement probe.
  • the drive motor 1810 may provide driving force to the single-axis stereotaxic frame via the drive cable 1815 (e.g., the second translation cable described above) that supports forward/retract translation motion.
  • 1820 e.g., the single-axis three-dimensional frame 1738 described above
  • a displacement sensor (not shown in the figure), installed on the single-axis three-dimensional frame 1820, can monitor the movement position of the LITT photon temperature measurement probe 1744.
  • the sensing signal of the displacement sensor is transmitted through the displacement sensor cable 1825.
  • the temperature sensing spectrum light signal measured by the LITT photon temperature measurement probe 1805 is sent to the temperature feedback control unit 1750 in real time through the LITT temperature measurement probe channel 1830.
  • the integrated component 1835 provides interface support for the portable connector mounted on the LITT temperature measurement probe channel 1830.
  • Figure 19 is a schematic diagram of a LITT photon ablation probe according to some embodiments of the present specification.
  • the LITT photon ablation probe may be a LITT photon lateral ablation probe 1910 or a LITT photon circumferential ablation probe 1920.
  • LITT photon lateral ablation probe 1910 may include an OCT probe 1912 and a LITT lateral ablation probe 1914.
  • LITT photon circumferential ablation probe 1920 may include an OCT probe 1922 and a LITT circumferential ablation probe 1924.
  • the LITT photon lateral ablation probe 1910 and the LITT photon circumferential ablation probe 1920 may each include a probe sleeve made of a specific material that is resistant to high temperatures and corrosion, such as polyetheretherketone (PEEK). )production.
  • PEEK polyetheretherketone
  • the LITT lateral ablation probe 1914 includes a probe body, a connection surface and a coating.
  • the connection surface is the connection interface between the body and the coating.
  • the probe body is cylindrical.
  • the probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • the end (distal end) of the probe body has a certain inclination angle (that is, the end surface of the probe body forms a certain angle with the axis of the probe body, and the included angle is an acute angle).
  • the connection surface is formed by smoothing the end surface of the probe body.
  • the plating uses noble metal (eg, gold, silver, and platinum group metals) target plating.
  • the coating layer may be formed by magnetron sputtering coating on the surface of the connection surface.
  • the coating of the LITT lateral ablation probe 1914 may be replaced with a lens (eg, a sapphire lens).
  • the end (distal end) of the probe body can be a straight surface or have a certain inclination angle (that is, the end surface of the probe body is perpendicular to or at a certain angle with the axis of the probe body, and the included angle is an acute angle) ).
  • the connection surface and the lens are welded by arc welding or high-temperature melting of tungsten (such as tungsten wire), iridium (such as iridium wire) and other materials, and the tungsten wire or iridium wire is selected for the high-temperature melting of tungsten or iridium.
  • the fire polishing process is to fire polish the welded surface.
  • the LITT circumferential ablation probe 1924 may include a probe body.
  • the probe body consists of a needle core and a hard cladding located on the outer periphery of the needle core.
  • the needle core is made of pure silicon dioxide material.
  • the hard cladding is made from Technology Enhanced Cladding Silica (TECS) material.
  • TECS Technology Enhanced Cladding Silica
  • a tapered surface is set at the far end of the probe body (the end closest to the target object.
  • the diameter of the tapered surface gradually decreases from the initial diameter to the preset diameter.
  • the tapered surface is provided with grooves, for example, formed by optical machine engraving. Laser light directed to the LITT circumferential ablation probe can emerge from the groove.
  • the grooves are evenly (dispersed) distributed along the tapered surface in a certain pattern shape (for example, thread shape) and do not overlap with each other.
  • the distribution pattern of the grooves is a single thread shape (spiral shape), a multi-thread cross shape (for example, a double thread cross), a rhombus grid shape, a honeycomb shape, etc., or a combination thereof.
  • LITT lateral ablation probe 1914 and LITT circumferential ablation probe 1924 are the same as or respectively the LITT lateral ablation probes 700, 800 and LITT circumferential ablation probe 900 described in Figures 6-11. Similar, will not be repeated here.
  • a drive motor 1930 may provide drive force via a drive cable 1935 (e.g., the first translation cable described above) that supports forward/retract translational motion, and a drive cable 1935 that supports rotational motion.
  • a drive cable 1935 e.g., the first translation cable described above
  • the driving cable 1940 (for example, the above-mentioned first rotation cable) provides driving force to the biaxial stereoscopic frame 1945 (for example, the above-mentioned biaxial stereoscopic frame 1736), so that the LITT photon ablation probe (such as the LITT photon lateral ablation probe 1910 or LITT photon circumferential ablation probe 1920) to perform translational and rotational two-degree-of-freedom movements, thereby reaching a specific position of the target object (for example, the position shown in FIG. 20), and performing LITT irradiation on the target object. .
  • a displacement sensor (not shown in the figure) provided on the biaxial three-dimensional frame 1945 can monitor the movement position of the LITT photon ablation probe.
  • the sensing signal of the displacement sensor is transmitted through the displacement sensor cable channel 1950.
  • the LITT lateral ablation probe 1914 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W)
  • the high-power ablation laser is placed on the outside of the target object by placing the LITT photon lateral ablation probe 1910 and shoots towards the target object in a certain direction.
  • the OCT probe 1912 in the LITT photon lateral ablation probe 1910 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time.
  • the OCT probe channel 1960 and the LITT ablation probe channel 1955 are integrated (eg, mechanically coupled) through an integration component 1965 .
  • the LITT circumferential ablation probe 1924 can receive the specific power transmitted by the LITT ablation probe channel 1955 (eg, 1-50W, 1-20W, 1-10W, 1-8W)
  • the high-power ablation laser is diffused through the groove on the LITT circumferential ablation probe 1924 and directed towards the target object (for example, cancerous tissue).
  • the OCT probe 1922 in the LITT photon circumferential ablation probe 1920 can scan and image the ablation status or pathological diagnosis of the target object in real time, and transmit it back to the OCT control module 1711 through the OCT probe channel 1960 in real time.
  • Figure 20 is a schematic diagram of a LITT photon ablation probe and a LITT photon temperature measurement probe during treatment according to some embodiments of this specification.
  • the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe can be placed in a preset Location.
  • the LITT photon temperature probe 2010 can obtain the temperature at a specific location on the edge of the target object.
  • the specific location may be the location furthest from the LITT photon ablation probe on the edge of the target object.
  • the distance between the LITT photon temperature measurement probe 2010 and the LITT photon ablation probe is smaller than the size of the target object.
  • the area within the edge of the target object may be, for example, irregularly shaped.
  • the target object may be equivalent to a circle.
  • the smallest circumscribed circle of the target object may be determined as the equivalent circle of the target object.
  • the size of the target object is, for example, the diameter of the equivalent circle.
  • the LITT photon ablation probe is a LITT photon circumferential ablation probe 2020
  • the LITT photon circumferential ablation probe 2020 (including the LITT circumferential ablation probe) is disposed on the
  • the LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon circumferential ablation probe 2020 on the edge of the target object.
  • the distance between the LITT photon circumferential ablation probe 2020 and the LITT photon temperature measurement probe 2010 is set to L dispersion .
  • L dispersion is equal to or close to the equivalent radius of the target object.
  • the equivalent radius here is the radius of the smallest circumscribed circle of the edge of the target object.
  • the LITT photon circumferential ablation probe 2020 is set at the equivalent center, and the LITT photon temperature measurement probe 2010 is set at the target object
  • the edge is the farthest position from the LITT photon circumferential ablation probe 2020, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature is from The equivalent center gradually decreases outward to ensure the therapeutic effect of the medical treatment device 1700.
  • the LITT photon lateral ablation probe 2030 (including the LITT lateral ablation probe) is disposed on one edge of the target object, so The LITT photon temperature measurement probe 2010 is disposed at the farthest position from the LITT photon lateral ablation probe 2030 on the edge of the opposite side of the target object.
  • the distance between the LITT photon lateral ablation probe 2030 and the LITT photon temperature measurement probe 2010 is set to L lateral direction .
  • L is laterally equal to or close to the equivalent diameter of the target object.
  • the equivalent diameter here is the diameter of the smallest circumscribed circle of the edge of the target object.
  • the photon temperature measurement probe 2010 is disposed on the edge of the opposite side of the target object at the farthest position from the LITT photon lateral ablation probe 2030, thus ensuring that the temperature within the entire range of the target object is higher than the predetermined temperature.
  • the temperature range is set to ensure the accuracy of temperature measurement, and the temperature gradually decreases from the side to the opposite side, thereby ensuring the treatment effect of the medical treatment device 1700.
  • the edge of the target object can be determined by using an image recognition or segmentation algorithm or model to process the MRI image containing the target object.
  • a typical image recognition or segmentation algorithm may include a convolution algorithm, that is, convolving image data with a specific operator to determine the edge contour in the image, where the specific operator may include a Roberts operator, a Sobel operator operator, Prewitt operator and zero-crossing Gaussian operator based on Laplacian operator.
  • the edge recognition algorithm may also include Canny detector, boosted edge learning algorithm (Boosted Edge Learning BEL) and other visual feature algorithms.
  • Boosted Edge Learning BEL boosted edge learning algorithm
  • Typical image recognition or segmentation models may include neural network models (e.g., deep learning models), generative adversarial networks (GAN), deep belief networks (DBN), stacked autoencoders (SAE), logistic regression (LR) models, support Vector machine (SVM) model, decision tree model, naive Bayes model, random forest model or restricted Boltzmann machine (RBM), gradient boosting decision tree (GBDT) model, Lambda MART model, adaptive enhancement model, Hidden Markov model, perceptron neural network model, Hopfield network model, etc. or any combination thereof.
  • the image recognition or segmentation model recognition is obtained by training historical images with target object edges in them as sample pairs.
  • the temperature feedback control unit 1750, the laser dose control unit 1760, the attenuator adjustment control unit 1770, the attenuator adjustment unit 1780 and the laser power controls the tissue temperature measured by the LITT photon thermometer probe 2010 to be in a preset temperature range (for example, 46 ⁇ 1°C).
  • the LITT circumferential ablation probe in the LITT photon circumferential ablation probe 2020 releases an ablation laser with a power of 1-8W and a characteristic wavelength of 1064nm to control the LITT photon temperature measurement probe 2010 always detects and based on the temperature feedback control unit 1750, laser dose control unit 1760, attenuator adjustment control unit 1770, attenuator adjustment unit 1780 and laser power attenuator 1790 feedback adjustment, the temperature at the location is within the preset temperature range.
  • the temperature of the tumor tissue adjacent to the LITT photon circumferential ablation probe 2020 will rise to nearly 100°C and rapidly coagulate and become necrotic, while the peripheral ring area will be an area where cells slowly undergo apoptosis for 48-72 hours or longer.
  • the laser light is continuously absorbed within the tissue, thereby generating continuous heat.
  • the higher temperature close to the LITT photon circumferential ablation probe 2020 causes cell membrane rupture and continued coagulation of proteins, resulting in continued instantaneous necrosis of the affected tissue.
  • the lower temperatures closer to the LITT photon thermoprobe 2010, which are causing the transition zone of apoptotic cells, can produce intermittent and ultimately death of immunogenic cells.
  • Beneficial effects that may be brought about by the embodiments of this specification include but are not limited to: (1) Temperature measurement by a remote thermocouple of the LITT probe that is more accurate than MRTI and/or temperature measurement by an FBG sensor, so that the temperature measurement performance of LITT can reach real-time Efficient feedback fully avoids damage caused by the distal end of the LITT probe and excessive tissue, reducing postoperative sequelae; (2)
  • the LITT ablation probe is used to carve cones and bevel carving processes to successfully create localized speckles that are smaller than the original ones.
  • the temperature feedback control unit 1750 laser dose control unit 1760, attenuator adjustment control unit 1770 (the three can be integrated into a processing module), attenuator adjustment unit 1780.
  • the laser power attenuator 1790 dynamically adjusts the current laser output dose value so that the temperature measured by the temperature measurement element is always within the preset temperature range, combined with the LITT photon temperature measurement probe that is more accurate than MRTI.
  • Treatment efficiency and success rate of device 1700 (9) Combined with the position setting of LITT photon circumferential ablation probe/LITT photon lateral ablation probe and LITT photon temperature measurement probe, combined with LITT photon temperature measurement that is more accurate than MRTI probe, thus ensuring that the temperature within the entire range of the target object is higher than the preset temperature range, thereby ensuring the accuracy of temperature measurement, and the temperature gradually decreases outward from the equivalent center, thereby ensuring that the medical treatment device 1700 healing effect.
  • numbers are used to describe the quantities of components and properties. It should be understood that such numbers used to describe the embodiments are modified by the modifiers "about”, “approximately” or “substantially” in some examples. Grooming. Unless otherwise stated, “about,” “approximately,” or “substantially” means that the stated number is allowed to vary by ⁇ 20%. Accordingly, in some embodiments, the numerical parameters used in the specification and claims are approximations that may vary depending on the desired features of the individual embodiment. In some embodiments, numerical parameters should account for the specified number of significant digits and use general digit preservation methods. Although the numerical ranges and parameters used to identify the breadth of ranges in some embodiments of this specification are approximations, in specific embodiments, such numerical values are set as accurately as is feasible.

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Abstract

L'invention concerne un dispositif de traitement médical. Le dispositif de traitement médical comprend un appareil d'imagerie par résonance magnétique (IRM), conçu pour imager une région spécifique comprenant un objet cible pour générer une image de résonance magnétique ; un appareil de thermothérapie laser interstitielle (LITT), qui comprend : une sonde de LITT, qui, sur la base de l'image de résonance magnétique, s'approche de l'objet cible et traite l'objet cible par émission laser ; et un élément de mesure de température, qui est intégré à la sonde de LITT pour former une sonde intégrée et est conçu pour acquérir la température de l'objet cible.
PCT/CN2022/123856 2022-07-02 2022-10-08 Dispositif de traitement médical et sonde de traitement Ceased WO2024060314A1 (fr)

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CN202211151254.4 2022-09-21
CN202211151254.4A CN117770947A (zh) 2022-09-21 2022-09-21 一种医学治疗装置
CN202211159480.7 2022-09-22
CN202211159480.7A CN117338407A (zh) 2022-07-02 2022-09-22 一种医学治疗装置及治疗探针
CN202211156542.9A CN117530770A (zh) 2022-08-02 2022-09-22 一种医学治疗装置及其测温元件和成像探针
CN202211156542.9 2022-09-22

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