Patent Application
20170050043
(a) Field of the Invention
The present invention relates to an optically diffusing fiber, a probe comprising the optically diffusing fiber, a method for manufacturing the same, and an optical fiber application device thereof. More specifically, the present invention relates to an optically diffusing fiber and an optically diffusing fiber probe capable of emitting light in a plurality of directions, a method for manufacturing the same, hybrid optical medical equipment for both diagnosis and treatment of tubular human tissue, a catheter-based laser treatment device, and an electromagnetic energy application device for tubular tissue stricture, comprising the optically diffusing fiber probe.
(b) Description of the Related Art
In general, optical fiber probe devices which emit light delivered through an inner core are widely utilized in various medical fields, and side surface emission type or front emission type optical fiber probes are mainly used. However, light emission in a fixed direction causes spatial restriction when treating an inner tissue of a human body.
Upon reviewing Korean and foreign markets for laser treatment, as the market in Korea focuses on the treatment for dermatological diseases, the use or development of optical fibers is in a poor condition. However, recently, as the demand for minimally invasive surgery increases and the market grows, an interest for the development of optical fibers increases. In the case of foreign markets, many investments in the development of front or side type optical fiber are done. The optical fibers are used for clinical treatments, for example, treatment for prostate, liposuction, treatment for periodontal diseases, etc.
However, most optical fiber probes emit light only in one direction. Thus, it is necessary to develop optical fiber probes for delivering electromagnet energy in various directions or in a fixed direction.
Asthma, which is a sort of tracheobronchial diseases, is an allergic disease caused by an allergic inflammatory response of sensitive bronchus. Asthma refers to a disease showing the following symptoms: Bronchial mucous membrane swells up by inflammation of bronchus forming an airway, bronchial muscle falls into a fit of convulsion, bronchus becomes narrow or blocked, which leads to dyspnea, wheezing and severe coughing. Due to environmental factors, more than 3 hundred million people in the world suffer from acute exacerbation of asthma, and every year, more than 250 thousand people die of the disease (2007, WHO). In the case of USA, for example, one person in the US spends about 3.7 million won for the treatment of asthma, and a total of 60 trillion won or more are estimated (2011, CDC). In the case of Korea, according to the Health Insurance Analysis Statistics in 2010 issued by the National Health Insurance Service, the number of patients with asthma gradually increases by 15% or more annually. Currently, it is estimated that more than 2.35 million people suffer from asthma, and annual socioeconomic costs incurred for asthma exceeds about 2.5 trillion won (2005, Korea Asthma Allergy Foundation).
In order to alleviate or treat symptoms of asthma, suction-type asthma therapeutic agents such as singulair or seretide, or oral-type asthma therapeutic agents are generally used. However, this kind of treatment using medicines temporarily alleviates symptoms. Since asthma needs to be continuously treated for a long time, the costs for treating asthma increases, it is inconvenient for patients with asthma, and side-effects and allergic reactions are often induced.
As a means for improving the above problems, RF surgery equipment for treating asthma was developed. In this regard, the Boston Scientific Corporation invented EP 01803409 entitled “System for treating tissue with radio frequency vascular electrode array.” Bronchial thermoplasty (product name) by the Boston Scientific Corporation involves induction of thermotherapy by delivering RF energy to the tissue where asthma occurs, by using a catheter, that is, Bronchial thermoplasty relates to a method delivering energy to a body tissue based on the delivery of electric current. However, Bronchial thermoplasty is expensive because of monopolistic supply of equipment, and accordingly, the costs for asurgery exceed 20 million won. Additionally, due to non-uniformimpedance within the body tissue, thermal damage often occurs. Accordingly, recovery is slow, pain is great, and recurrence rate is high, which gives a great burden on patients and medical systems.
Conventional methods for treating trachea include tracheal resection, balloon dilation, stenting and surgery using tracheostomy tube (T-tube), etc. As to the conventional methods for treating trachea, due to the occurrence of scar by an invasive surgery, there is a high possibility that tracheal stricture could recur. Additionally, the conventional methods cause damage on surrounding tissues due to hemorrhage or photothermal treatment, and have a high risk in inflammation and infection. Thus, most of them simply exhibit temporary treatment effects. In the case of the balloon dilation, a fixed size of airway may be temporarily secured by the expansion of balloon. However, due to contraction of tissue, re-stricture could easily occur. Also, a result of surgery and a period for recovery greatly depend on skills and experience of an operator.
Thus, it is urgently necessary to develop treatment equipment capable of performing medicinal treatment in combination therewith, in order todecreasea recurrence rate of contraction and minimize complications such as inflammation, infection, etc. which could occur during recovery, by expanding the part of trachea where stricture occurs and permanently modifying a structure of tissue simultaneously.
Meanwhile, a conventional laser treatment uses a method of inserting an optical fiber delivering laser into a varix and generating heat using optical energy, thereby contracting blood vessels and detouring obstructed blood flow. However, in order to minimize thermal damage and medical accidents, a user who uses laser treatment equipment needs to have a lot of surgery experience and high surgery capacity, and thus this treatment is restrictive and difficult to be performed. Especially, the conventional laser treatment causes intravascular perforation by optical fiber which directly contacts a blood vessel or lacks uniform thermal delivery, and thus recurrence and medical accidents occur due to insufficient treatment or excessive treatment.
In general, before performing trachea surgery, information on the degree of stricture in the trachea is obtained using a computed tomography (CT). However, CT has a limitation that a prognosis cannot be accurately and rapidly monitored therefrom. Thus, it is necessary to provide a diagnosis means capable of increasing treatment efficiency and securing stability, by obtaining a change in tissue right after treatment through real-time imaging according to depth and length of stricture of trachea.
The present invention is to solve the conventional problems as above. The present invention aims to provide a probe comprising an optically diffusing fiber capable of emitting light in a plurality of directions unlike the conventional optical fiber, and thus capable of constantly emitting electromagnetic energy in a plurality of directions to tubular tissue diseases or solid cancers, such as thyroid cancer, breast cancer, kidney cancer, etc., to treat a broader range of diseases in a safe and efficient way, and a method for manufacturing the same.
Also, the present invention aims to provide hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, capable of inducing photothermal treatment for tubular human tissues, such as trachea, blood vessel, ureter, etc., by a single human activating module including an optically diffusing fiber installed to penetrate into the inside of the probe, and performing real-time monitoring on an OCT image for the human tissue during a process for inducing photothermal treatment, thereby allowing integrated diagnosis and induction of treatment for a lesion tissue to be made while minimizing the damage on the human tissue.
Also, the present invention aims to provide hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue capable of performing macroscopic monitoring of a tubular human tissue using a camera and an optical source module for photographing during the process of inducing laser photothermal treatment using an optically diffusing fiber, a side type optical fiber arranged in a predetermined pattern, a single mode optical fiber, etc. and microscopic monitoring of a tubular human tissue by obtaining an OCT image, thereby allowing precise diagnosis and induction of treatment for an initial lesion in the tubular tissue.
Also, the present invention aims to provide a catheter-based laser treatment device capable of preventing recurrence of trachea stricture, minimizing complications such as inflammation, infection, etc. which may occur during recovery, and treating a part to be treated during treatment while monitoring the part in real-time.
Also, the present invention aims to provide an electromagnetic energy application device for tubular tissue stricture capable of minimizing hemorrhage through blood vessels before and after and during the treatment by using an expansion of various balloon catheters with a geometric shape, inducing blood vessel stricture without contraction of balloon catheter, and including a fixed shape of balloon catheter from which deflation may be induced according to vasoconstriction during laser treatment.
The above-described objects may be achieved by technical resolutions below.
An optically diffusing fiber, including: a fabrication length of a tissue treatment section required for laser treatment; a tapering angle and an end diameter within the fabrication length capable of uniformly delivering optical energy; a fabrication angle and fabrication part interval capable of varying optical energy distribution delivered; and a height of an optically diffusing surface fabricated to vary a diffusion range of optical energy.
An optical fiber probe for treating a tubular tissue disease or a solid cancer including the optically diffusing fiber.
A method for manufacturing an optically diffusing fiber probe, which includes the steps of (a) inputting fabrication values including an optically diffusing range according to a disease part to be treated, energy distribution, optical fiber fabrication length, tapering angle, end diameter, fabrication angle, fabrication part interval, and height of an optically diffusing surface for manufacturing a suitable optical fiber for treatment length, etc.; (b) outputting a fabrication control signal through a fabrication controlling part; (c) fabricating a side surface and front end of an optical fiber by moving the optical fiber in the rotational direction and front and back direction according to the fabrication control signal; (d) delivering optical energy to an optical fiber; (e) measuring optical energy delivered to the side surface and front end of an optical fiber through a side surface optical sensor and a front optical sensor; and (f) determining whether to go through additional fabrication and polishing by comparing the measured strength and the pre-stored energy distribution of the optical fiber.
The method for manufacturing an optically diffusing fiber probe, wherein the step (f) further includes the step of conducting a feedback for precise fabrication when determined to go through an additional fabrication, and fabrication delivery speed, rotational speed, and fabrication energy are minutely controlled during the precise fabrication.
The method for manufacturing an optically diffusing fiber probe, wherein the step (a) of inputting the fabrication values further includes the step (a-1) of controlling the fabrication length L of the optical fiber in consideration of the tissue treatment section required for laser treatment, and the step (a-1) determines an initial fabrication location of the optical fiber with an overall fabrication length in consideration of a translational stage.
The method for manufacturing an optically diffusing fiber probe, wherein the step (a) of inputting the fabrication values for the optical fiber to be fabricated further includes the step (a-2) of determining the tapering angle α and end diameter d of the optical fiber so that light of the optical energy is uniformly delivered through the optical fiber, and the step (a-2) determines the tapering angle α and end diameter d of the optical fiber by simultaneously or independently controlling the translational speed, rotational speed, power of fabrication energy source (0.1 W to 50 W), and area of energy source of the optical fiber.
The method for manufacturing an optically diffusing fiber probe, wherein the step (a) of inputting fabrication values for the optical fiber to be fabricated further includes the step (a-3) of determining a fabrication angle β and a fabrication part interval w to vary the optical energy distribution delivered through the optical fiber, and the step (a-3) determines the fabrication angle β and fabrication part interval w by simultaneously or independently controlling the translational speed and rotational speed of the optical fiber.
The method for manufacturing an optically diffusing fiber probe of the above 7, wherein the step (a) of inputting fabrication values for the optical fiber to be fabricated further includes the step (a-4) of determining the height p of the optically diffusing surface to vary the diffusion range of optical energy light through the optical fiber, and the step (a-4) determines the height p of the optically diffusing surface by controlling the rotational speed of the optical fiber, power of fabrication energy source (0.1 W to 50 W) and area of energy source.
Hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, which includes a probe moving by being inserted in a tubular human tissue; a human activating optical fiber module protruding to the front end of the probe by passing an inner passage of the probe, the human activating optical fiber module performing any one selected from obtaining an optical coherence tomography (OCT) image of a tubular human tissue through infrared light emission of a predetermined wavelength area and inducing tubular human tissue photothermal treatment through laser emission; a controller connected to the human activating optical fiber module, performing the operation control of the human activating optical fiber module for obtaining an OCT image of human tissue and for inducing human tissue photothermal treatment; and an OCT image output device connected to the controller, outputting an OCT image obtained from the human activating optical fiber module, wherein OCT image monitoring on the tubular human tissue and laser stimulation thereon are performed integrally.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the human activating optical fiber module performing tubular human tissue photothermal treatment inducement through the laser emission includes an optically diffusing fiber.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the human activating optical fiber module includes an optical fiber for diagnosis emitting near infrared ray in a wavelength range of 800 to 1550 nm to a tubular human tissue and inducing obtainment of an OCT image for a predetermined part of a tubular human tissue through location adjustment by near infrared ray emission by translational movement and rotational movement; and an optical fiber for treatment emitting laser of a predetermined wavelength to a lesion part of a tubular human tissue in a predetermined pattern, and stimulating the lesion part through location adjustment by laser emission by translational movement and rotational movement, wherein the optical fiber for treatment is at least one selected from one optically diffusing fiber emitting near infrared ray from an entire part of an outer circumference, and at least one side type optical fiber emitting near infrared ray only to a predetermined area limited in the lateral direction.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the human activating optical fiber module includes an optical fiber integrated coating body formed of a penetrating path for movably receiving the optical fiber for diagnosis and optical fiber for treatment independently, so that the optical fiber integrated coating body passes the inner passage of the probe.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the optically diffusing fiber is inserted into a balloon-shaped catheter passing through the inner passage of the probe and protruding to the front end of the probe, the balloon-shaped catheter having a balloon-shaped expansion tube arranged expandably at the end.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the human activating optical fiber module includes a single mode optical fiber which emits at least one selected from near infrared ray in a wavelength range of 800 to 1550 nm and laser of a predetermined wavelength to a tubular human tissue, controls the emission location by translational movement and rotational movement, and integrally performs inducement of obtainment of an OCT image for a predetermined part of the tubular human tissue and stimulation of a lesion part of the tubular human tissue.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, which further includes a camera having a photographing lens forming exposure towards the front end of the probe; and an optical source module for photography emitting visible rays through optical source bodies forming exposure towards the front end of the probe, thereby performing macroscopic monitoring of a tubular human tissue through a tubular human tissue image photographed by the camera and microscopic monitoring of the tubular human tissue through the OCT image, simultaneously.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the controller includes a controller for tissue diagnosis performing the operation control of the human activating optical fiber module for obtaining an OCT image of a human tissue; and a controller for laser treatment performing the operation control of the human activating optical fiber module for inducing photothermal treatment of the human tissue, and allowing Q-switched laser or pulse type laser in a wavelength of 532 nm, 980 nm, and 1470 nm to be emitted on a tubular human tissue having hemoglobin over a predetermined level.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the controller includes a controller for tissue diagnosis for performing the operation control of the human activating optical fiber module for obtaining an OCT image of a human tissue; and a controller for laser treatment performing the operation control of the human activating optical fiber module for inducing photothermal treatment of the human tissue, and allowing Q-switched frequency-doubled Nd:YAG 532 nm laser to be emitted on a tubular human tissue having blood vessel over a predetermined level.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, wherein the controller includes a controller for tissue diagnosis for performing the operation control of the human activating optical fiber module for obtaining an OCT image of a human tissue; and a controller for laser treatment performing the operation control of the human activating optical fiber module for inducing photothermal treatment of the human tissue, and allowing laser in a wavelength of 800 nm to be emitted on a tubular human tissue injected with a bio-dye material, indocyanine green.
A catheter-based laser treatment device, which includes: a catheter; a balloon having an inner space interconnected with the catheter, connected to an end of the catheter enabling expansion and contraction; a pressure controlling part inserting or discharging operation fluid to introduce the operation fluid into the balloon or discharge the operation fluid from the balloon through the catheter; an optical fiber inserted into the balloon penetrating through the catheter; a laser system transmitting laser through the optical fiber; a side type optical fiber inserted into the balloon penetrating through the catheter; and an imaging system transmitting and receiving light through the side type optical fiber to obtain an image of a tissue with the balloon inserted.
The catheter-based laser treatment device, wherein the optical fiber inserted into the balloon penetrating through the catheter is an optically diffusing fiber.
The catheter-based laser treatment device, wherein the pressure controlling part inserts or discharges the operation fluid at a pressure of 1 to 15 psi.
The catheter-based laser treatment device, wherein the pressure controlling part vibrates the balloon at a frequency of 1 to 100 Hz while maintaining a constant pressure.
The catheter-based laser treatment device, wherein the pressure controlling part generates a vibration wave, and the vibration wave is delivered to the balloon through the operation fluid.
The catheter-based laser treatment device, wherein at least one substance selected from the group consisting of an anti-inflammatory material, anti-infective material and anti-oxidation material having physiological compatibility is coated or impregnated on the surface of the balloon.
The catheter-based laser treatment device, wherein the pressure controlling part controls the insertion or discharge speed of the operation fluid so that the expansion and contraction speed of the balloon is 10 to 1000 μm/sec.
The catheter-based laser treatment device, wherein the pressure controlling part vibrates the balloon, simultaneously when the laser system emits laser to the tissue through the optical fiber.
An electromagnetic energy application device for tubular tissue stricture, which includes a catheter; a balloon catheter having an inner space interconnected with the catheter, connected to an end of the catheter enabling expansion and contraction; a pressure controlling part inserting or discharging operation fluid to introduce the operation fluid into the balloon catheter or discharge the operation fluid from the balloon catheter through the catheter; an optical fiber inserted into the balloon catheter penetrating through the catheter; a laser system transmitting laser through the optical fiber; and a location moving part withdrawing the balloon catheter.
The electromagnetic energy application device for tubular tissue stricture, wherein the optical fiber inserted into the balloon penetrating through the catheter is an optically diffusing fiber.
The electromagnetic energy application device for tubular tissue stricture, wherein the front end of the balloon catheter is formed in a sharp funnel shape, or the front and rear ends are symmetrically formed in a sharp funnel shape.
The electromagnetic energy application device for tubular tissue stricture, wherein the pressure controlling part inserts or discharges the operation fluid at a pressure of 1 to 15 psi.
The electromagnetic energy application device for tubular tissue stricture, wherein the pressure controlling part vibrates the balloon catheter at a frequency of 1 to 100 Hz while maintaining a constant pressure.
The electromagnetic energy application device for tubular tissue stricture, wherein the pressure controlling part generates a vibration wave, and the vibration wave is delivered to the balloon catheter through the operation fluid.
The electromagnetic energy application device for tubular tissue stricture, wherein the pressure controlling part controls the insertion or discharge speed of the operation fluid so that the expansion and contraction speed of the balloon catheter is 10 to 1000 μm/sec.
The electromagnetic energy application device for tubular tissue stricture, wherein the pressure controlling part vibrates the balloon catheter, simultaneously when the laser system emits laser to the tissue through the optical fiber.
The present invention provides an optically diffusing fiber capable of emitting light in a plurality of directions and a method for manufacturing the same, and a probe including the optically diffusing fiber for treating tubular tissue diseases or solid cancers (thyroid cancer, breast cancer kidney cancer, etc.) When using the optically diffusing fiber according to the present invention, electromagnetic energy could be constantly emitted in a plurality of directions, thereby treating a broader range of diseases in a safe and efficient way.
Also, the present invention may be applied to photothermal treatment or photodynamic therapy through insertion into an inner tissue of a human body by using an optically diffusing fiber capable of emitting light in a plurality of directions. Additionally, the optically diffusing fiber may be used for treating thyroid cancer, breast cancer, prostate cancer, kidney cancer, bladder cancer, brain tumor, inner uterine wall, localized liver cancer, skin cancer, cancer tissue, coagulation of inner tissue, removal of fat, etc.
Also, according to hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue according to the present invention, obtainment of an OCT image for the tubular human tissue such as bronchus, blood vessel and ureter, and induction of photothermal treatment of human tissue by laser may be integrally performed through a single probe, thereby increasing efficiency of lesion diagnosis of tubular human tissue and induction of treatment. Also, the OCT image for the human tissue may be monitored in real time before and after performing the induction of photothermal treatment of human tissue, thereby efficiently performing diagnosis for lesion tissue and induction of treatment while minimizing damage on the human tissue. Especially, according to hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue of the present invention, diagnosis for various respiratory diseases such as asthma and induction of treatment may be promoted. Furthermore, the equipment may be applied to various surgery fields, so the usability thereof could be increased.
Additionally, a catheter-based laser treatment device according to the present invention has effects of preventing tracheal stricture from recurring after surgery, and minimizing complications such as inflammation, injection, etc. which may occur during recovery. Also, the catheter-based laser treatment device performs treatment while monitoring in real time a part to be treated during treatment, thereby minimizing damage on tissue caused by the photothermal treatment.
According to the present invention, the use of various balloon catheters with geometric shape may minimize hemorrhage through blood vessels before or during treatment by using expansion of the balloon catheters, and induce vascular stricture without contraction of the balloon catheters.
In addition, according to the present invention, the use of a fixed shape of balloon catheter allows automatic induction of deflation of catheter according to vasoconstriction during laser treatment.
The present invention relates to an optically diffusing fiber probe, a method for manufacturing the same, and an application thereof. More specifically, the present invention relates to an optically diffusing fiber probe capable of emitting light in a plurality of directions and a method for manufacturing the same, and hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue, a catheter-based laser treatment device, and an electromagnetic energy application device for tubular tissue stricture, including the optically diffusing fiber probe.
1. An Optically Diffusing Fiber Probe and a Method for Manufacturing the Same
The first aspect of the present invention relates to an optically diffusing fiber, an optical fiber probe for treating a tissue disease or a solid cancer including the optically diffusing fiber, and a method for manufacturing the same.
The optically diffusing fiber according to the present invention has a fabrication length L of a tissue treatment section required for laser treatment; a tapering angle α and an end diameter d within the fabrication length capable of uniformly delivering optical energy; a fabrication angle β and fabrication part interval w capable of varying optical energy distribution delivered; and a height p of an optically diffusing surface fabricated to vary a diffusion range of optical energy.
The optically diffusing fiber probe for treating a tissue disease or a solid cancer according to the present invention includes an optically diffusing fiber as described above.
Additionally, a method for manufacturing an optically diffusing fiber probe for treating a tissue disease or a solid cancer according to the present invention includes the steps of (a) inputting fabrication values including an optically diffusing range according to a disease part to be treated, energy distribution, optical fiber fabrication length L, tapering angle α, end diameter d, fabrication angle β, fabrication part interval w, and height p of optically diffusing surface for manufacturing a suitable optical fiber for treatment length, etc.; (b) outputting a fabrication control signal through a fabrication controlling part; (c) fabricating a side surface and a front end of an optical fiber by moving the optical fiber in the rotational direction and front and back direction according to the fabrication control signal; (d) delivering optical energy to an optical fiber; (e) measuring optical energy delivered to the side surface and front end of an optical fiber through a side surface optical sensor and a front optical sensor; and (f) determining whether to go through additional fabrication and polishing by comparing the energy distribution of the measured strength and pre-stored optical fiber.
According to the present invention, as to the fabrication length L, the initial fabrication location of the optical fiber is determined together with an entire fabrication length in consideration of a translational stage. The tapering angle α and end diameter d of the optical fiber is determined by simultaneously or independently controlling the translational speed, rotational speed, power of fabrication energy source (0.1 W to 50 W), and area of energy source of the optical fiber. The fabrication angle β and fabrication part interval w are determined by simultaneously or independently controlling the translational speed and rotational speed of the optical fiber. The height p of the optically diffusing surface is determined by controlling the rotational speed of the optical fiber, power of fabrication energy source (0.1 W to 50 W) and area of energy source.
In the method for manufacturing the optically diffusing fiber for treating a tissue disease or a solid cancer according to the first aspect of the present invention, the step (f) may further include the step of conducting a feedback for precise fabrication when determined to go through an additional fabrication, and the precise fabrication minutely controls fabrication delivery speed, rotational speed, and fabrication energy.
The step (a) may further include the step (a-1) of controlling the fabrication length L of the optical fiber in consideration of the tissue treatment section required for laser treatment, and the step (a-1) determines an initial fabrication location of the optical fiber with an overall fabrication length in consideration of a translational stage.
The step (a) may further include the step (a-2) of determining the tapering angle α and end diameter d of the optical fiber so that light of the optical energy is uniformly delivered through the optical fiber, and the step (a-2) determines the tapering angle α and end diameter d of the optical fiber by simultaneously or independently controlling the translational speed, rotational speed, power of fabrication energy source (0.1 W to 50 W), and area of energy source of the optical fiber.
The step (a) may further include the step (a-3) of determining a fabrication angle β and a fabrication part interval w to vary the optical energy distribution delivered through the optical fiber, and the step (a-3) determines the fabrication angle β and fabrication part interval w by simultaneously or independently controlling the translational speed and rotational speed of the optical fiber.
The step (a) may further include the step (a-4) of determining the height p of the optically diffusing surface to vary the diffusion range of optical energy light through the optical fiber, and the step (a-4) determines the height p of the optically diffusing surface by controlling the rotational speed of the optical fiber, power of fabrication energy source (0.1 W to 50 W) and area of energy source.
Hereinafter, embodiments of the optically diffusing fiber, the optical fiber probe for treating a tissue disease or a solid cancer including the optically diffusing fiber, and a method for manufacturing the same according to the first aspect of the present invention will be explained in detail with reference to the accompanying drawings. First, in adding reference numerals to constitutional elements of each drawing, the same constitutional element is to have the same reference numeral, if possible, even though the constitutional element is illustrated in another drawing. Additionally, when it is determined that detailed explanation on related well-known constitution or function may make the gist of the present invention unclear, the detailed explanation thereon will be omitted. Additionally, hereinafter, preferred embodiments of the present invention will be explained, but it is of course that the technical idea of the present invention is not limited thereto, but can be carried out by a skilled person in the art.
As illustrated in
Here, an optical fiber generally includes a core providing a path through which light is delivered and a cladding surrounding the core. In the present invention, both a single-mode optical fiber and a multi-mode optical fiber may be used according to transmission type of light.
An optically diffusing fiber probe according to the present invention may be manufactured by using an optical fiber probe manufacturing device 100 including an optical fiber holder 10, a fabrication controlling part 20, an optical fiber fabrication part 30, a side surface optical sensor 50, a front optical sensor 40, and an optical providing part 60.
The optical fiber holder 10 installs an optical fiber, which is the object to be fabricated. A rotational motor, which is not illustrated, is driven according to a control signal of the fabrication controlling part 20 to rotate the optical fiber.
The fabrication controlling part 20 outputs a fabrication control signal which controls the optical fiber holder 10 and the optical fiber fabrication part 30 based on predetermined fabrication values in consideration of optically diffusing range of light, energy distribution, treatment length, etc., for the optical fiber to be fabricated.
The optical fiber fabrication part 30 fabricates and polishes an optical fiber, which is the object to be fabricated, installed on the optical fiber holder 10. The optical fiber fabrication part fabricates and polishes the optical fiber by driving the rotational motor, which is not illustrated, according to the fabrication control signal to move towards side surface and front surface of the optical fiber.
The optical energy providing part 60 provides optical energy to an optical fiber fabricated and is delivered through the optical fiber holder 10. The side surface optical sensor 50 and the front optical sensor 40 are installed at the side surface or front end of the optical fiber to measure a strength of optical energy, to confirm whether the optical energy delivered from the optical energy providing part 60 is smoothly emitted to the side surface and front end of the optical fiber.
The fabrication controlling part 20 compares the strength of optical energy measured from the side surface optical sensor 50 and front optical sensor 40 with the predetermined energy distribution of the optical fiber to determine whether to add fabrication and polishing.
The fabrication controlling part 20 applies and controls the fabrication control signal, which minutely controls the fabrication delivery speed, rotational speed, fabrication energy, etc. for optimizing the optical fiber, to the optical fiber holder 10 and the optical fiber fabrication part 30.
As illustrated in
To this end, the method for manufacturing the optically diffusing fiber probe according to the present invention installs an optical fiber to be fabricated on the optical fiber holder 10 (S10), and inputs fabrication values through a monitor and a key input part, which are not illustrated, in consideration of light diffusing range, energy distribution, treatment length, etc., for the optical fiber to be fabricated (S20).
When the input of the fabrication values is completed, the fabrication controlling part 20 outputs a fabrication control signal which controls the optical fiber holder 10 and the optical fiber fabrication part 30 (S30), and the optical fiber holder 10 drives the rotational motor (not illustrated) according to the fabrication control signal to rotate the optical fiber installed on the optical fiber holder 10 (S40).
The optical fiber fabrication part 30 moves in the front and back direction according to the fabrication control signal, and fabricates and polishes the side surface and front end of the optical fiber installed on the optical fiber holder 10 (S40).
When the fabrication and polishing of the optical fiber is completed by the optical fiber fabrication part 30, the optical energy is delivered to the fabricated optical fiber using the optical energy providing part 60, and whether the optical energy provided from the optical energy providing part 60 is delivered to the side surface and front end of the optical fiber is measured by the side surface optical sensor 50 and front optical sensor 40 (S50).
The fabrication controlling part 20 compares the strength measured by the side surface optical sensor 50 and front optical sensor 40 with the pre-stored energy distribution of the optical fiber to determine whether to go through additional fabrication and polishing (S60).
In the step S60, when it is determined to go through additional fabrication and polishing by the fabrication controlling part 20, a feedback process for precise fabrication is performed (S70). Here, as to the precise fabrication, the fabrication controlling part 20 applies the fabrication control signal, which minutely controls again fabrication delivery speed, rotational speed, fabrication energy, etc., to the optical fiber holder 10 and optical fiber fabrication part 30. Thus, the step S30 is repetitively performed.
Meanwhile, a process of inputting fabrication values in consideration of light diffusing range for the optical fiber to be fabricated, energy distribution, treatment length, etc. (S20) is as below.
First, the optical fiber fabrication length L is adjusted in consideration of tissue treatment section required for laser treatment. Here, an initial fabrication location of the optical fiber is determined with an entire fabrication length in consideration of a translational stage.
Thereafter, a tapering angle α and a diameter d of the optical fiber end are determined so that light of optical energy can be uniformly delivered through the optical fiber. For example, the tapering angle α and diameter d of the optical fiber end are determined by simultaneously or independently controlling the translational speed, rotational speed, power of fabrication energy source (0.1 W to 50 W), and area of energy source of the optical fiber.
Also, in order to vary the optical energy distribution delivered through the optical fiber, a fabrication angle β and a fabrication part interval w are determined. For example, the fabrication angle β and fabrication part interval w are determined by simultaneously or independently controlling the translational speed and rotational speed of the optical fiber.
Also, in order to vary the light diffusing range of optical energy through the optical fiber, a height p of the optically diffusing surface fabricated is determined. For example, the height p of the optically diffusing surface is determined by controlling the rotational speed of the optical fiber, power of fabrication energy source (0.1 W to 50 W) and area of energy source.
Thereafter, whether light of optical energy provided from the optical energy providing part (light source, 60) through the optical fiber side surface fabrication is uniformly delivered to all directions through the side surface and front end of the optical fiber.
As illustrated in
Here, the fabrication angle of the optical fiber surface is controlled to between 0° and 90° according to light diffusing range of optical energy. At an angle of 0°, a partial optical emission is possible radially (ring type), and at an angle of 90°, a partial optical emission is possible axially (it is possible to induce emission in all directions at an angle between 0° and 90°).
In order to determine the optical energy distribution, the optically diffusing fiber probe adjusts a size of optically diffusing surface (i.e., diameter) formed in a side surface of the optical fiber to between 0.01 mm and 0.4 mm, and adjusts the fabrication depth, interval of optically diffusing surface, power of fabrication energy source, area of energy source, etc., to determine the size of optically diffusing surface.
As the surface size of the optically diffusing fiber probe is smaller, a higher density of energy distribution is possible. As the size thereof is greater, a relatively lower density of optical energy distribution is possible. The fabrication length of the optical fiber can be determined according to the size of optical energy tissue treatment (i.e., 0.5 to 5 cm).
For uniformly distributing electromagnetic energy, the optically diffusing fiber probe fabricates tapering of the optical fiber, performs side surface energy distribution focusing inducement at the end according to the angle (15 to 75°) of the tapering, and adjusts the fabrication translational speed to within a range of 0.5 to 10 mm/s for tapering fabrication.
By tapering the diameter of the end of the optical fiber between 0.05 to 0.2 mm, loss at the end of the optical energy can be reduced within 5%. Additionally, by tapering the diameter of the end of the optical fiber between 0.2 to 0.8 mm, 10 to 50% of entire optical energy can be emitted at the end in front direction.
The optically diffusing fiber probe determines the degree of fabrication of the optical fiber core and cladding according to desired electromagnetic energy distribution, controls the fabrication rotational speed to within 60 to 500 rpm according to the cladding removal range, and simultaneously or independently controls the fabrication energy to 0.1 W to 50 W and fabricate the energy.
Here, for partial and selective optical diffusion (deep fabrication depth: 0.05 to 0.5 mm), slow speed (10 to 200 rpm) is applied, and for broad optical diffusion (swallow surface fabrication: 0.01 to 0.05 mm), fast speed (200 to 1000 rpm) is applied.
Also, the optically diffusing fiber probe determines distribution and directional properties of optical energy in a desired direction according to the side surface and surface fabrication processing of the optical fiber. Here, the electromagnetic energy distribution includes Flat-top, Gaussian, Left-skewed, Right-skewed, Fractional, Diffuse, Radial, etc.
The directional properties of the electromagnetic energy include Front, Fractional, Cylindrical, Spherical, etc. Additionally, the fabrication interval is controlled to between 0.05 and 0.8 mm for controlling distribution form of optical energy, and the fabrication translational speed is controlled to between 0.5 and 10 mm/s for uniform energy distribution according to an axis of optical fiber.
The optically diffusing fiber probe uses non-contact mechanical or electromagnetic energy source for optical fiber surface fabrication. Here, the electromagnetic energy source includes femto second, picosecond, ultraviolet laser, arc discharge, etc. The fabrication power is adjusted to within 0.01 to 50 W to induce a change in the fabrication degree of the optical fiber surface. Additionally, the fabrication surface of the optical fiber can be polished using the energy source after fabricating the optical fiber for continuous optical diffusion.
The optically diffusing fiber probe determines a method for processing a side surface and a surface of the optical fiber according to desired distribution of electromagnetic energy. The side surface energy distribution form may be implemented with flat-top or Gaussian, by making the size of optically diffusing surface greater (diameter of 0.1 to 0.3 mm) at an end and a starting end of the optical fiber, and making the size of optically diffusing surface smaller (diameter of 0.05 to 0.09 mm) at a center portion.
The optically diffusing fiber probe uses an energy sensor to identify energy distribution of fabricated optical fiber, and carries out fabrication optimization. Here, when the length of optical fiber is 1 cm or greater, the fabrication size and fabrication depth per section of optical fiber are changed to induce uniform energy distribution in the lateral direction. Additionally, the fabrication size and depth are changed every length within 15 to 40% of the entire optical fiber to constantly maintain energy distribution at an end and a starting end of the optical fiber.
The optically diffusing fiber probe is inserted into the tissue disease, and may induce photothermal coagulation, photodynamic therapy, or tissue removal for desired tissue. Additionally, the optically diffusing fiber can be used for treating thyroid cancer, breast cancer, prostate cancer, kidney cancer, bladder cancer, brain tumor, inner uterine wall, localized liver cancer, skin cancer, cancer tissue, coagulation of inner tissue, removal of fat, etc.
As described above, the present invention manufactures an optical fiber probe capable of emitting light in a plurality of directions unlike the conventional optical fiber, which simply emits light in a fixed direction (front or side) to constantly emit electromagnetic energy in a plurality of directions to a tubular tissue disease or a solid cancer (thyroid cancer, breast cancer, kidney cancer, etc.), thereby treating a broader range of diseases in a safe and efficient way.
2. Hybrid Optical Medical Equipment for Both Diagnosis and Treatment of a Tubular Human Tissue.
The second aspect of the present invention relates to hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue using a probe including an optically diffusing fiber.
The hybrid optical medical equipment for both diagnosis and treatment of tubular human tissue according to the present invention includes a probe moving by being inserted in a tubular human tissue; a human activating optical fiber module protruding to the front end of the probe by passing an inner passage of the probe, the human activating optical fiber module performing any one selected from obtaining an optical coherence tomography (OCT) image of a tubular human tissue through infrared light emission of a predetermined wavelength area and inducing tubular human tissue photothermal treatment through laser emission; a controller connected to the human activating optical fiber module, performing the operation control of the human activating optical fiber module for obtaining an OCT image of human tissue and for inducing human tissue photothermal treatment; and an OCT image output device connected to the controller, outputting an OCT image obtained from the human activating optical fiber module.
According to one embodiment of the hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue according to the present invention, the human activating optical fiber module may include an optical fiber for diagnosis inducing obtainment of an OCT image for a predetermined part of a tubular human tissue through location adjustment by near infrared ray emission by translational movement and rotational movement, the human activating optical fiber module emitting near infrared ray in a wavelength range of 800 to 1550 nm to a tubular human tissue; and an optical fiber for treatment emitting laser of a predetermined wavelength to a lesion part of a tubular human tissue in a predetermined pattern, and stimulating the lesion part through location adjustment by laser emission by translational movement and rotational movement.
The optical fiber for treatment may be at least one selected from one optically diffusing fiber emitting near infrared ray from an entire part of an outer circumference, and at least one side type optical fiber emitting near infrared ray only to a predetermined area limited in the lateral direction. The optically diffusing fiber may be inserted into a balloon-shaped catheter passing through the inner passage of the probe and protruding to the front end of the probe, and the balloon-shaped catheter may have a balloon-shaped expansion tube arranged expandably at the end.
It is preferable that the human activating optical fiber module includes an optical fiber integrated coating body formed of a penetrating path for movably receiving the optical fiber for diagnosis and optical fiber for treatment independently, so that the optical fiber integrated coating body passes the inner passage of the probe.
According to another embodiment of the present invention, the human activating optical fiber module includes a single mode optical fiber which emits at least one selected from near infrared ray in a wavelength range of 800 to 1550 nm and laser of a predetermined wavelength to a tubular human tissue, controls the emission location by translational movement and rotational movement, and integrally performs inducement of obtainment of an OCT image for a predetermined part of the tubular human tissue and stimulation of a lesion part of the tubular human tissue.
The hybrid optical medical equipment for both diagnosis and treatment of a tubular human tissue according to another embodiment of the present invention further includes a camera having a photographing lens forming exposure towards the front end of the probe; and an optical source module for photography emitting visible rays through optical source bodies forming exposure towards the front end of the probe, thereby performing macroscopic monitoring of a tubular human tissue through a tubular human tissue image photographed by the camera and microscopic monitoring of the tubular human tissue through the OCT image, simultaneously.
According to another embodiment of the present invention, the controller includes a controller for tissue diagnosis performing the operation control of the human activating optical fiber module for obtaining an OCT image of a human tissue; and a controller for laser treatment performing the operation control of the human activating optical fiber module for inducing photothermal treatment of the human tissue, the controller for laser treatment allowing Q-switched laser or pulse type laser in a wavelength of 300 to 3000 nm to be emitted on a tubular human tissue having hemoglobin over a predetermined level, Q-switched frequency-doubled Nd:YAG 532 nm laser to be emitted on a tubular human tissue having blood vessel over a predetermined level, or laser in a wavelength of 800 nm to be emitted on a tubular human tissue injected with a bio-dye material, indocyanine green.
Hereinafter, embodiments of the present invention will be explained in detail with reference to
As illustrated in
The probe 210 moves by being inserted into a tubular human tissue such as bronchus, blood vessel, and ureter. As the probe 210, a probe included in an endoscope or a bronchoscope may be used.
The human activating optical fiber module 220 protrudes to the front end of the probe 210 by passing an inner passage 211 of the probe 210. This human activating optical fiber module 220 obtains an OCT image of a tubular human tissue through infrared ray emission of a predetermined wavelength area, and induces photothermal treatment of the tubular human tissue through laser emission. Here, the OCT image obtainment of the tubular human tissue through infrared ray emission is performed during and before and after inducement of photothermal treatment of the tubular human tissue through laser emission. By obtaining the OCT image of the tubular human tissue, a change in smooth muscle under an epithelial cell may be observed, and the degree of treatment of a lesion part and the degree of thermal damage of the tubular human tissue may be observed in real time.
The human activating optical fiber module 220 according to the embodiment of the present invention includes an optical fiber for diagnosis 221 and an optical fiber for treatment 222. Independent inducement of the movements (translational movement and rotational movement) of the optical fiber for diagnosis 221 and the optical fiber for treatment 222 allows real-time diagnosis and treatment inducement for the tubular human tissue.
The optical fiber for diagnosis 221 emits near infrared ray in a wavelength range of 800 to 1550 nm to the tubular human tissue; and obtains the OCT image for a predetermined part of the tubular human tissue through location adjustment by near infrared ray emission by translational movement and rotational movement. As such, the optical fiber for diagnosis 221 is configured to emit near infrared ray to a predetermined area limited in the lateral direction as shown in
The optical fiber for treatment 222 emits laser of a predetermined wavelength to a lesion part of a tubular human tissue in a predetermined pattern, and stimulates the lesion part through location adjustment by laser emission by translational movement and rotational movement. At least one optical fiber for treatment 222 is selected from at least one optically diffusing fiber 2221 and at least one side type optical fiber 2222, and the constitution of the optical fiber for treatment 222 is determined according to a structure of lesion part of the tubular human tissue and treatment thickness required.
The optically diffusing fiber 2221, which is an optical fiber allowing near infrared ray to be emitted from an entire part of an outer circumference surface, is used when photothermal coagulation of overall tubular human tissue is required. The optically diffusing fiber 2221 has short optical penetrating depth properties and constant laser energy distribution properties, and thus may allow limited and uniform treatment inducement for a human tissue.
The side type optical fiber 2222, which is an optical fiber allowing near infrared ray to be emitted only to a predetermined area limited in the lateral direction, is used when photothermal coagulation of a part of tubular human tissue is required. The side type optical fiber 2222 may deliver high laser energy, and thus it is used when incision of human tissue or coagulation of relatively thick human tissue is required.
According to an embodiment of the present invention, the human activating optical fiber module 220 may include the optical fiber for diagnosis 221, and the optical fiber for treatment 222 including the optically diffusing fiber 2221, as illustrated in
The optically diffusing fiber 2221 forming the optical fiber for treatment 222 may pass an inner passage 211 of the probe 210 to be inserted into the inside of a balloon-shaped catheter 225 protruding toward the front end of the probe 210. By the balloon-shaped catheter 225, swift and safe human tissue treatment inducement may be possible while inducing uniform temperature increase in all directions. Here, the balloon-shaped catheter 225 has balloon-shaped expansion tubes 2251 and 2251′ disposed expandably to an end. The balloon-shaped expansion tubes 2251 and 2251′ may be expanded through saline solution, thereby modifying the balloon-shaped expansion tubes 2251 and 2251′ in accordance with structural characteristics of the tubular human tissue.
The balloon-shaped expansion tubes 2251 and 2251′ have an inner space interconnected with the inner passage of the balloon-shaped catheter 225. According to the embodiment of the present invention, the balloon-shaped catheter 225 has the balloon-shaped expansion tube 2251 formed to be extended from an end as illustrated in
Additionally, a glass cap is fitted into an end of the optically diffusing fiber 2221 so that the end of the optical fiber could be protected, and laser emitted from the optically diffusing fiber 2221 is uniformly diffused to all directions without directional properties.
According to an embodiment of the present invention, in the human activating optical fiber module 220, the optical fiber for diagnosis 221 and the optical fiber for treatment 222 are connected to an OCT device 226 and electromagnetic energy device 227 as illustrated in
The human activating optical fiber module 220 according to another embodiment of the present invention has one single mode optical fiber 223 as illustrated in
The single mode optical fiber 223 selectively emits near infrared ray in the wavelength of 800 to 1550 nm or laser with a predetermined wavelength to a tubular human tissue. The single mode optical fiber 223 may integrally perform the OCT image obtainment for a predetermined part of the tubular human tissue and stimulation for a lesion part of the tubular human tissue, while controlling emission location through the translation movement and rotational movement.
Meanwhile, according to an embodiment of the present invention, as illustrated in
A controller 230 is connected to the human activating optical fiber module 220, and performs the operation control of the human activating optical fiber module for obtaining an OCT image of human tissue and the operation control of the human activating optical fiber module for inducing photothermal treatment of human tissue. For this, the controller 230 includes a controller for tissue diagnosis 231 and a controller for laser treatment 232. The controller for tissue diagnosis 231 controls the operation of human activating optical fiber module for obtaining the OCT image of human tissue. The controller for laser treatment 232 controls the operation of the human activating optical fiber module for inducing photothermal treatment of human tissue.
The controller for laser treatment 232 may allow Q-switched laser or pulse type laser in a wavelength of 300 to 3000 nm to be emitted on a tubular human tissue having hemoglobin over a predetermined level through the human activating optical fiber module 220. Additionally, the controller for laser treatment 232 may allow Q-switched frequency-doubled Nd:YAG 532 nm laser to be emitted on tubular human tissue having blood vessel over a predetermined level through the human activating optical fiber module 220. By minimum invasion from the pulse type laser in a short wavelength, the lesion part of tubular human tissue may be removed.
When it is necessary to clearly distinguish the lesion part of tubular human tissue, indocyanine green, which is a bio-dye material, or dye inducing optical absorption reaction may be injected into a tubular human tissue so that treatment efficiency could be increased when inducing laser photothermal treatment. In this case, the controller for laser treatment 232 allows the laser in the wavelength of 800 nm to be emitted to the tubular human tissue to which indocyanine green, bio-dye material, through the human activating optical fiber module 220.
An OCT image output device 240 is connected to the controller 230 to output an OCT image obtained from the human activating optical fiber module 220.
A camera 250 has a photographing lens 251 forming exposure towards the front end of the probe 210 as illustrated in
An optical source module for photography 260 emits visible rays through optical source bodies 261 forming exposure towards the front end of the probe 210, as illustrated in
Here, the hybrid optical medical equipment 200 for both diagnosis and treatment of tubular human tissue according to an embodiment of the present invention may perform macroscopic monitoring of a tubular human tissue through a tubular human tissue image photographed by the camera 250 and microscopic monitoring of the tubular human tissue through the OCT image output by the OCT image output device 240.
The hybrid optical medical equipment 200 for both diagnosis and treatment of tubular human tissue according to an embodiment of the present invention configured as above induces photothermal treatment for tubular human tissues such as bronchus, blood vessel, and ureter through the human activating optical fiber module 220 installed by passing through the inside of the single probe 210, and performs real-time monitoring of OCT image for human tissue during and before and after the inducement of photothermal treatment of human tissue by the same human activating optical fiber module 200, thereby integrally performing diagnosis and treatment inducement for a lesion part while minimizing damage on human tissue. Additionally, the hybrid optical medical equipment 200 for both diagnosis and treatment of tubular human tissue according to the embodiment of the present invention includes the optical fiber for diagnosis 221 and the optical fiber for treatment 222. As the translation movement and rotational movement of the optical fiber for diagnosis 221 and the optical fiber for treatment 222 are independently induced to allow real-time diagnosis and treatment inducement for tubular human tissue. By performing macroscopic monitoring of tubular human tissue through the camera 250 and optical source module for photography 260 and microscopic monitoring of tubular human tissue through the obtained OCT image simultaneously, during and before and after inducement of laser photothermal treatment by the optically diffusing fiber 221, side type optical fiber 222 disposed in a predetermined pattern, single mode optical fiber 223, etc., the present invention allows precise diagnosis and treatment for an initial lesion within tubular tissues which was difficult to be treated with the conventional technology.
3. A Catheter-Based Laser Treatment Device
The third aspect of the present invention relates to a catheter-based laser treatment device, which includes a catheter; a balloon having an inner space interconnected with the catheter, connected to an end of the catheter enabling expansion and contraction; a pressure controlling part inserting or discharging operation fluid to introduce the operation fluid into the balloon or discharge the operation fluid from the balloon through the catheter; an optical fiber inserted into the balloon penetrating through the catheter; a laser system transmitting laser through the optical fiber; a side type optical fiber inserted into the balloon penetrating through the catheter; and an imaging system transmitting and receiving light through the side type optical fiber to obtain an image of a tissue with the balloon inserted.
The pressure controlling part inserts or discharges the operation fluid at a pressure of 1 to 15 psi.
Additionally, the pressure controlling part vibrates the balloon at a frequency of 1 to 100 Hz while maintaining a constant pressure.
Also, the pressure controlling part generates a vibration wave, and the vibration wave is delivered to the balloon through the operation fluid.
Also, at least one substance selected from the group consisting of an anti-inflammatory material, anti-infective material and anti-oxidation material having physiological compatibility is coated or impregnated on the surface of the balloon.
Also, the pressure controlling part controls the insertion or discharge speed of the operation fluid so that the expansion and contraction speed of the balloon is 10 to 1000 μm/sec.
Also, the pressure controlling part vibrates the balloon, simultaneously when the laser system emits laser to the tissue through the optical fiber.
Hereinafter, preferred embodiments of the catheter-based laser treatment device according to the present invention will be explained in detail with reference to the drawings attached.
Hereinafter, the catheter-based laser treatment device 300 according to preferred embodiment of the present invention will be explained with reference to
The catheter-based laser treatment device 300 according to a preferred embodiment of the present invention includes a catheter 310, a balloon 320, a pressure controlling part 330, an optical fiber 340, a laser system 345, a side type optical fiber 350, and an imaging system 355.
The catheter 310 is formed in a tubular shape and inserted into the body, and the optical fiber 340 and side type optical fiber 350 are inserted through the inner penetrating path.
The balloon 320 has an inner space interconnected with the catheter 310, and connected to an end of the catheter 310 enabling expansion and contraction.
The balloon 320 is formed of a material from which laser ray emitted through the optical fiber 340 is penetrated into the tissue to be treated.
Additionally, an anti-inflammatory material, anti-infective material and anti-oxidation material having physiological compatibility is coated or impregnated on the surface of the balloon 320.
The balloon 320 where the drug is coated or impregnated on its surface is inserted into trachea and is expanded so that the drug could be delivered to the tissue to be treated while contacting a part to be treated in trachea.
As the drug is delivered to the part to be treated along with photothermal treatment by the laser ray, the complications such as inflammation, infection, etc. of the tissue to be treated would be minimized.
The drug coated on the surface of the balloon 320 is not limited to an anti-inflammatory anti-infective, anti-oxidant material. Any material may be coated or impregnated if the material is useful for the treatment.
The pressure controlling part 330 inserts or discharges the operation fluid to expand or contract the balloon 320 through the catheter 310 to introduce the operation fluid into the balloon 320 or discharge the operation fluid from the balloon 320.
In this case, the operation fluid, for example, consists of fluid which is harmless to human body even if it is inserted into trachea like air or saline solution. Additionally, the pressure controlling part 330 and catheter 310 are directly connected, or interconnected through an additional conduit so that the operation fluid could be flowed through the conduit.
The pressure controlling part 330 may be implemented with means such as a pump inserting or discharging the operation fluid. Preferably, the pressure controlling part may be implemented with an electronic pump capable of precisely controlling the amount of insertion or discharge of the fluid according to a predetermined speed.
Specifically, the pressure controlling part 330 controls the speed of insertion or discharge of the operation fluid so that the speed of expansion and contraction of the balloon 320 could be 10 to 1000 μm/sec.
Additionally, the pressure controlling part 330 is capable of expanding or contracting the balloon 320 by inserting or discharging the operation fluid with a pressure of 1 to 15 psi.
The pressure controlling part 330 allows the balloon 320 to be expanded or contracted with various speeds and pressures. Additionally, the balloon 320 gives or releases the pressure to the tissue coagulated by the laser ray so that the corresponding tissue could be expanded or permanently modified.
At this time, when the speed of expansion and contraction of the balloon 320 is less than 10 μm/sec, the expansion and contraction speed are very slow, and thus it would be difficult to induce modification of tissue within a given time. When the speed of expansion and contraction exceeds 1000 μm/sec, the speed is excessively fast, and thus it would not be easy to control the pressure of the balloon 320 and the tissue could be damaged by a sudden expansion pressure.
Also, when the pressure expanding and contracting the balloon 320 is less than 1 psi, the pressure is so low, and thus it would be difficult to induce modification. It is possible to sufficiently modify the tissue in the trachea under the pressure below 15 psi, so the pressure exceeding 15 psi is unnecessary. The pressure exceeding 15 psi may excessively press the tissue so the tissue could be damaged.
Furthermore, the pressure controlling part 330 is configured to vibrate the balloon 320 at a frequency of 1 to 100 Hz while maintaining a constant pressure. The pressure controlling part 330 causes periodical expansion and contraction of coagulated tissue through the balloon 320 so that the trachea may permanently and easily control the size modified and modification rate.
For this, the pressure controlling part 330 may include a means for generating a vibration wave (not illustrated) generating a vibration wave, and the vibration wave generated by this is delivered to the balloon 320 through the operation fluid.
The pressure controlling part 330 is capable of repetitively inserting and discharging a small amount of operation fluid to the balloon 320 according to a fixed time interval in order to vibrate the balloon 320 with a fixed interval.
The optical fiber 340 is passed through the catheter 310. Additionally, one end thereof is inserted into the inside of the balloon 320, and the laser system 345 transmitting the laser through the optical fiber 340 is disposed at another end of the optical fiber 340.
The optical fiber 340 is formed of the optically diffusing fiber. Additionally, the probe or glass cap for diffusing or condensing laser ray with a proper form according to the necessity may be included in the one end of the optical fiber 340.
The laser system 345 is connected to the optical fiber 340 to supply laser ray, and the laser system 345 controls the wavelength of laser ray, emission strength and emission interval according to the properties of tissue to be treated.
The pulsed laser and continuous wave laser (cw laser) may be used as laser supplied to the optical fiber 340 by the laser system 345. As the wavelength of laser, a visible ray wavelength, a near infrared ray wavelength, a medium infrared wavelength, a far infrared ray wavelength, etc. may be applied.
In this case, the laser system 345 may include a laser diode capable of modulating an output signal in order to control emission strength of laser ray through which the degree of penetration of laser ray into the tissue to be treated and temperature may be precisely controlled.
Meanwhile, the side type optical fiber 350 passes through the catheter 310 like the optical fiber 340, and one end thereof is inserted into the inside of the balloon 320. Another end of the side surface optical fiber 350 is connected to the imaging system 355, and the imaging system 355 transmits and receives light or optical signal through the side surface optical fiber 350 to obtain an image of tissue of a part to which the balloon 320 is inserted.
Here, the imaging system 355 may be implemented an image photographing device such as an optical coherence tomography (OCT) device, a photoacoustic tomography device, a polarization imaging device, etc.
Additionally, the side type optical fiber 350 may be coupled to the optical fiber 340 inside the catheter 310 or balloon 320, and this allows the surface type optical fiber 350 to perform translational and rotational movement along with the optical fiber 340.
As the side type optical fiber 350 is coupled to the optical fiber 340 to be moved and rotated together, the laser emitted through the optical fiber 340 is emitted to the tissue, and thus a photocoagulation process of tissue could be monitored in real time. For this real-time monitoring, it would be unnecessary to further operate the side surface optical fiber 350 and move it.
As illustrated in
In this case, the pressure controlling part 330 allows the drug on the surface of balloon 320 to be delivered to the target tissue by allowing the laser system 345 to emit laser to the tissue through the optical fiber 340 or vibrating the balloon 320 with a time difference, simultaneously.
Additionally, the catheter-based treatment device 300 according to the preferred embodiment of the present invention may perform monitoring by the side type optical fiber 350 right after or simultaneously with laser emission as illustrated in
Meanwhile, it was explained as an example that the catheter-based treatment device 300 according to preferred embodiments of the present invention is used in the treatment of trachea. However, it is of course that the catheter-based treatment device 300 of the present invention may be used for the treatment of all tubular human tissues other than trachea.
4. Electromagnetic Energy Application Device for Tubular Tissue Stricture
The fourth aspect of the present invention relates to anelectromagnetic energy application device for tubular tissue stricture, which includes a catheter; a balloon catheter having an inner space interconnected with the catheter, connected to an end of the catheter enabling expansion and contraction; a pressure controlling part inserting or discharging operation fluid to introduce the operation fluid into the balloon catheter or discharge the operation fluid from the balloon catheter through the catheter; an optical fiber inserted into the balloon catheter penetrating through the catheter; a laser system transmitting laser through the optical fiber; and a location moving part withdrawing the balloon catheter.
According to the present invention, the front end of the balloon catheter is formed in a sharp funnel shape, or the front and rear ends are symmetrically formed in a sharp funnel shape.
The pressure controlling part of the present invention inserts or discharges the operation fluid at a pressure of 1 to 15 psi.
The pressure controlling part of the present invention vibrates the balloon catheter at a frequency of 1 to 100 Hz while maintaining a constant pressure.
The pressure controlling part generates a vibration wave, and the vibration wave is delivered to the balloon catheter through the operation fluid.
The pressure controlling part controls the insertion or discharge speed of the operation fluid so that the 1 and contraction speed of the balloon catheter is 10 to 1000 μm/sec.
The pressure controlling part vibrates the balloon catheter, simultaneously when the laser system emits laser to the tissue through the optical fiber.
Hereinafter, preferred embodiments of the electromagnetic energy application device for tubular tissue stricture according to the present invention will be explained in detail with reference to the drawings attached.
Hereinafter, the electromagnetic energy application device for tubular tissue stricture according to preferred embodiments of the present invention will be explained with reference to
The electromagnetic energy application device for tubular tissue stricture according to the preferred embodiment of the present invention includes a catheter 310, a catheter balloon 420, a pressure controlling part 430, an optical fiber 440, a laser system 445, and a location moving part 450.
The catheter 410 is formed in a tubular shape and inserted into the body, and the optical fiber 440 is inserted through the inner penetrating path.
The balloon catheter 420 has an inner space interconnected with the catheter 410, and connected to an end of the catheter 410 to be form as expandable or contractible balloon.
The balloon catheter 420 is formed of a material from which laser ray emitted through the optical fiber 440 is penetrated into the tissue to be treated.
Additionally, the balloon catheter 420 is formed in geometrically various shapes, for example, the front end of the balloon catheter is formed in a sharp funnel shape, or the front and rear ends are symmetrically formed in a sharp funnel shape.
As illustrated in
In this case, the operation fluid, for example, consists of fluid which is harmless to human body if it is inserted into trachea like air or saline solution. Additionally, the pressure controlling part 430 and catheter 410 are directly connected, or interconnected through an additional conduit so that the operation fluid could be flowed through the conduit.
The pressure controlling part 430 may be implemented with means such as a pump inserting or discharging the operation fluid. Preferably, the pressure controlling part may be implemented with an electronic pump capable of precisely controlling the amount of insertion or discharge of the fluid according to a predetermined speed.
Specifically, the pressure controlling part 430 controls the speed of insertion or discharge of the operation fluid so that the speed of expansion and contraction of the balloon catheter 420 could be 10 to 1000 μm/sec.
Additionally, the pressure controlling part 430 is capable of expanding or contracting the balloon 420 by inserting or discharging the operation fluid with a pressure of 1 to 15 psi.
The pressure controlling part 430 allows the balloon 420 to be expanded or contracted with various speeds and pressures. Additionally, the balloon 420 gives or releases the pressure to the tissue coagulated by the laser ray so that the corresponding tissue could be expanded or permanently modified.
At this time, when the speed of expansion and contraction of the balloon 420 is less than 10 μm/sec, the expansion and contraction speed are very slow, and thus it would be difficult to induce modification of tissue within a given time. When the speed of expansion and contraction exceeds 1000 μm/sec, the speed is excessively fast, and thus it would not be easy to control the pressure of the balloon 420 and the tissue could be damaged by a sudden expansion pressure of the balloon catheter 420.
Also, when the pressure expanding and contracting the balloon 420 is less than 1 psi, the pressure is so low, and thus it would be difficult to induce modification. It is possible to sufficiently modify the tissue in the trachea under the pressure below 15 psi, so the pressure exceeding 15 psi is unnecessary. The pressure exceeding 15 psi may excessively press the tissue so the tissue could be damaged.
Furthermore, the pressure controlling part 430 is configured to vibrate the balloon 420 at a frequency of 1 to 100 Hz while maintaining a constant pressure. The pressure controlling part 430 causes periodical expansion and contraction of coagulated tissue through the balloon 420 so that the trachea may permanently and easily control the size modified and modification rate.
For this, the pressure controlling part 430 may include a means for generating a vibration wave (not illustrated) generating a vibration wave, and the vibration wave generated by this is delivered to the balloon 420 through the operation fluid.
The pressure controlling part 430 is capable of repetitively inserting and discharging a small amount of operation fluid to the balloon 420 according to a fixed time interval in order to vibrate the balloon 420 with a fixed interval.
The optical fiber 440 is passed through the catheter 410. Additionally, one end thereof is inserted into the inside of the balloon 420, and the laser system 445 transmitting the laser through the optical fiber 440 is disposed at another end of the optical fiber 440.
The optical fiber 440 is formed of the optically diffusing fiber. Additionally, the probe or glass cap for diffusing or condensing laser ray with a proper form according to the necessity may be included in the one end of the optical fiber 440.
The laser system 445 is connected to the optical fiber 440 to supply laser ray, and the laser system 440 controls the wavelength of laser ray, emission strength and emission interval according to the properties of tissue to be treated.
The pulsed laser and continuous wave laser (cw laser) may be used as laser supplied to the optical fiber 440 by the laser system 445. As the wavelength of laser, a visible ray wavelength, a near infrared ray wavelength, a medium infrared wavelength, far infrared ray wavelength, etc. may be applied.
In this case, the laser system 445 may include a laser diode capable of modulating an output signal in order to control emission strength of laser ray through which the degree of penetration of laser ray into the tissue to be treated and temperature may be precisely controlled.
The location moving part 465 includes a step motor, etc., which is not illustrated, to move a location of the balloon catheter 420 in the back direction. Additionally, after operation, the location moving part withdraws the balloon catheter 420 within the blood vessel.
As illustrated in
Here, the imaging system 450 may be implemented with an image photographing device such as an optical coherence tomography (OCT) device, a photoacoustic tomography device, a polarization imaging device, etc.
Accordingly, the electromagnetic energy application device for tubular tissue stricture according to the present invention may perform monitoring by the imaging system 450 right after or simultaneously with laser emission which allows an operator to conduct photocoagulation more precisely and stably.
As illustrated in
Furthermore, the energy of laser supplied to the optical fiber 440 by the laser system 445 may be changed in consideration of various diameters, lengths, etc. of the blood vessel to control the amount of coagulation, thereby providing more convenient treatment technology.
Meanwhile, it was explained as an example that the electromagnetic energy application device for tubular tissue stricture according to the present invention was used for the treatment of trachea. However, it is of course that the electromagnetic energy application device for tubular tissue stricture according to the present invention may be used for the treatment of all tubular human tissues other than trachea.
The electromagnetic energy application device for tubular tissue stricture according to the present invention as described above uses various balloon catheters with geometric shapes to minimize hemorrhage by the blood vessel before or during the treatment using the expansion of balloon catheter, and induce stricture of blood vessel without contraction of the balloon catheter. Additionally, the electromagnetic energy application device for tubular tissue stricture may use a fixed form of balloon catheter to automatically induce deflation of catheter according to contraction of blood vessel during laser treatment.
Menorrhagia is an abnormality of having excessive bleeding from the uterus during a woman's menstrual cycle. On average, 30% of women experience heavy uterine bleeding at some time in their lifetime. Symptoms of menorrhagia may include heavy, prolonged or irregular periods of more than 80 ml blood loss. Women with menorrhagia can be treated medically with oral contraceptive pills, nonsteroidal anti-inflammatory drugs, and androgenic steroids, etc. However, these medications are often associated with various side effects as well as temporary relief. In order to seek a more permanent solution, surgical treatment alternatives have also been performed. A definitive treatment for menorrhagia and other gynecological diseases is a hysterectomy, removal of the uterus. Nevertheless, the procedure is quite radical and invasive, with possible accompanying hemorrhage, long recovery time, high infection rate, bowel obstruction, and even sudden hormonal change. Thus, patients with menorrhagia often pursue alternatives to hysterectomy.
As a less invasive treatment option, hysteroscopic endometrial ablation has instead been performed to treat menorrhagia by using a number of techniques such as thermal balloon, cryotherapy, bipolar radiofrequency, and microwave ablation. Endometrial hyperplasia is one of the major causes of heavy menstrual bleeding. Thus, throughout the ablative techniques, the endometrium, which is the innermost layer of the uterus, is surgically removed without damaging the myometrium, the outer layer of the endometrium in order to maintain fertility. In spite of minimally invasive procedures, these treatments are still technically difficult and may result in thermal injury to peripheral tissue, eventually leading to various complications and unwanted sterility. In addition, the procedures require a series of treatments of at least 10 minutes to complete endometrial ablation, postoperatively leaving severe pain. Evidently, surgeons still need a way to complete endometrial destruction without the need for general anesthesia, surgical intervention, and complications.
Due to their high degree of accuracy and safety, fiber-based lasers have proved to be useful tools to ablate the endometrium with varying degrees of success. A variety of wavelengths, including 805 nm for diode, 1064 nm for Nd:YAG, 1320 nm for Nd:YAG, and 2.12 μm for Ho:YAG, have been used for endometrial ablation. Through direct irradiation of optical energy, the endometrium can be coagulated due to light absorption and resultant heat accumulation, leading to coagulation necrosis. The diode laser presented overall tissue effects similar to those of Nd:YAG lasers, both experimentally and clinically in light of tissue necrosis. However, low absorption coefficients, particularly at near-IR (1064 and 1320 nm), resulted in deep optical penetration depth up to 5 mm in soft tissue (for water, optical penetration depth=1/absorption coefficient=1/0.1 cm-1=10 cm) and thus irreversible thermal damage into the deep tissue, entailing hemorrhage at the surface of the uterus. In addition, the lasers of 805, 1064, and 1320 nm were operated in the continuous wave (CW) mode, so irreversible thermal injury was aggravated by protracted irradiation time and long heat diffusion. Under the irrigation environment, the mid-IR wavelength (2.12 μm) was readily associated with transmission loss on account of saline absorption (absorption coefficient=70 cm-1), so the laser would require higher input power for efficient light delivery. Furthermore, end-firing fibers could hardly achieve uniform tissue coagulation due to their small numerical aperture (N.A.) to cover the endometrium surface and difficulty in maneuvering the fiber during laser ablation.
In an attempt to obtain homogeneous light distribution, an optical diffuser has been developed and evaluated for endometrial ablation. The diffuser was created by removing the cladding and adding a diffusing medium such as silicon and scattering particles on the core surface. However, the applied power level (≦25 W) was relatively lower than the requirement for surgical tissue removal. In addition, the procedure was cumbersome because it required long irradiation time as well as administration of photosensitizers into a body prior to the operation, in comparison with surgical treatments. To prevent the risk of melting a diffuser, particularly under high power application, a balloon catheter was also developed and used together with a near-IR laser for treatment. Since the laser heated the balloon material directly rather than the targeted tissue, indirect heating was induced to the endometrium layer, which needed the real-time monitoring of temperature inside the tissue with thermocouples for safety purpose. Additionally, a 1064 nm wavelength with deep optical penetration (˜5 mm) at lower power (20 W) contributed to long irradiation time (10 to 12 min), deep coagulation necrosis (up to 4 mm), and undesirable hemorrhage.
In the current study, an endoscopic optical diffuser was designed and developed for minimally invasive endometrial ablation with a visible wavelength. Due to high vasculature in the uterus, an effective wavelength of 532 nm was selected to target hemoglobin in blood vessels and glandular tissue in the endometrium and, in essence, to treat menorrhagia. A 1-mm core fiber was directly micro-machined to create scattering segments for light diffusion. The balloon catheter was incorporated with the diffuser in order to achieve fast and uniform heat distribution as well as to provide structure integrity during the treatment. Light propagation from the diffuser was optically simulated, and the designed diffusing device was evaluated in vitro and in vivo in terms of coagulation time and necrosis thickness. The prototype device was also validated with a cadaveric human uterus to see its clinical applicability.
In an attempt to predict photon distribution from the designed diffusing tip, optical simulation (Zemax) was conducted to demonstrate light intensity and its spatial distribution at various distances. Two fiber conditions were compared: a bare diffuser tip and a glass-capped diffuser tip. To model the light scattered from the fiber surface, a Lambertian diffuser model was used with one million of rays and a light source with uniform angular distribution. The diffusing tip was exclusively modeled with surface scattering (i.e., ˜50 μm size scattering segment). The applied wavelength was 532 nm with the input power of 120 W, and the entire fiber length was 1.5 m including a 25 mm diffusing part at the tip. A 40×50 mm planar detector was placed underneath the diffusing fiber at distances of 1, 5, and 10 mm to identify light propagation and the spatial distribution of the scattered photons in two-dimensional (2-D). The profiles of light intensity were also measured and quantitatively compared between the two fiber conditions.
Bovine liver tissue was used as a tissue model for in vitro tests with the designed diffusing fibers, in that the chromophores, such as dead endothelial cells and blood vessels, would still be able to absorb the visible laser light (wavelength=532 nm) significantly. The liver specimens were acquired from a local slaughter house, and they were cut into 5×7 cm segments in size and 1 cm thick and stored at 4° C. prior to the experiments.
Three mature female Saanen goats were used for in vivo retrograde laser coagulation studies. Animal procedures and care were conducted in accordance with a protocol approved by American Preclinical Service (APS) Institutional Animal Care and Use Committee (IACUC). Experiments, necropsy, and histology were performed at APS, and all surgical procedures were performed with the animals under general endotracheal anesthesia. A caprine uterus is typically bicornuate so two prominent uterine horns come together to form a short uterine body. Thus, six caprine uteri in total were tested for the current photocoagulation tests. Similar to a human uterus, the caprine uterine wall consists of two major tissue layers: endometrium and myometrium. The endometrium is a pseudostratified layer of epithelium on the luminal surface of the uterus, containing richly vascular loose connective tissue along with fibroblasts, macrophages, and mast cells, etc. The myometrium is two layers of smooth muscle separated by the stratum vasculare, which is a zone of large vessels (arteries, veins, and lymph vessels). For the current in vivo studies, the prototype device was evaluated to photocoagulate solely the endometrial layer, in that any thermal injury to the myometrium would adversely affect fertility. The prototype device consisted of a capped diffusing fiber, a PUR balloon catheter, a customized inflating tube (1 cm outer diameter and 8 cm long), and a customized inflating pump (variable pressure levels from 1 to 7 psi). The 4-cm long catheter device was inserted into the animal uterus, and the balloon catheter was distended with saline until it securely held the uterine wall (i.e., approximately 3 cm in balloon diameter at 5 psi). A 532 nm clinical laser was used with the input power of 120 W, and the irradiation time was approximately 30 s, based upon in vitro results (i.e., applied energy=3600 J and irradiance=3.2 W/cm2 assuming a 3-mm thick endometrium for photocoagulation). Postoperatively, all the animals were euthanized 2 h after the tests by euthasol injection. Immediately after euthanasia, each uterine horn was removed, fixed in 10% neutral buffered formalin, and embedded in paraffin for hematoxylin and eosin (H&E) staining. From histology images, the thickness of coagulation necrosis was measured with Image J (n=18) and evaluated quantitatively.
A human uterus was donated by a 59-year-old postmenopausal patient for research at APS after a radical hysterectomy. The cadaveric uterus was used to evaluate the feasibility of the prototype device in terms of light leaking and deployment of fiber and balloon during laser irradiation. The device was inserted through the cervix for minimally invasive uterine access, and a 5-cm long balloon catheter was distended at 4 psi by saline. The balloon catheter was approximately 1.8 cm in balloon diameter. The applied power of 120 W was irradiated on the uterine wall for approximately 20 s (i.e., applied energy=2400 J and irradiance=4.2 W/cm2) as the distance between the fiber and tissue was closer than the in vivo condition due to the rigidity of the cadaveric tissue. The degree of coagulation necrosis in the tissue was also examined postexperimentally with Image J (n=12). A digital camera (9.1M DSC-H50, Sony) was used to take images of pre-, intra-, and postoperation to show a sequence of photocoagulation. A Student's t-test was also used for statistical analysis and p<0.05 meant statistically significant.
After in vitro validation of various diffusing fiber conditions, the design for the capped diffusing fiber was finalized, and the prototype optical device was made and incorporated with a balloon catheter for in vivo and cadaver studies as shown in
Followed by in vivo studies, a cadaveric human uterus was tested with the prototype device (2400 J, 4.2 W/cm2,
Spatial distribution of photons between diffusing and capped diffusing fibers were simulated and compared at various distances (
A capped diffusing fiber with PUR induced rapid and wide tissue coagulation as shown in
Based upon the assumption that an endometrial layer was 3 mm thick, the irradiation time for in vivo experiments was selected as 30 s to generate the coagulation thickness comparable to the endometrium thickness [
Considering a typical uterus volume, the estimated average irradiance on the entire uterus surface area (i.e., 88 cm2 assuming a uterine cavity as a frustum of right circular cone) would be 1.3 W/cm2 under 120-W application. The estimated value is approximately 70% lower than the irradiance (4.2 W/cm2) used for the cadaver study. Thus, one may need a longer irradiation time in order to achieve the comparable coagulation thickness. Moreover, since the uterus is a closed volume, diffuse reflection from the uterine wall could take place to uniformly distribute the diffusely scattered light, subsequently expanding thermal diffusion. Accordingly, one may have to take into account the effect of diffuse scattering on the uterine wall in an attempt to determine the appropriate irradiation time for clinical tests. It was also noted that a certain part of the treated tissue was superficially carbonized [
Since a cylindrical shape of the balloon catheter was used to make the prototype, the entire surface of the endometrium hardly achieved the uniform coagulation. Moreover, the anatomy of human uterus seems triangular. In an attempt to resolve the current challenges such as free movement of fiber tip and diverse uterus geometry, the new design for the optical device has been suggested and under investigation (
The current study demonstrated the laser irradiation time on the order of seconds to treat endometrial cell layers (
The feasibility of the newly designed diffusing optical device was demonstrated for endometrial treatment. Due to the wide distribution of photons with high irradiance, the new optical diffuser was incorporated into a balloon catheter facilitated photocoagulation globally, compared to other minimally invasive techniques. The optical response of uterine tissue to 532 nm irradiation confined tissue coagulation to endometrial cell layers without any thermal injury to myometrium, unlike Nd:YAG lasers that cause deep coagulation necrosis. The uniform and rapid development of coagulation (2 to 3 mm thick) evidenced that the balloon catheter-based optical diffuser can be exploited to treat heavy menstrual bleeding as a simple and safe therapeutic device. Further development of the proposed design may provide a more efficient and safer tool for gynecologists to treat menorrhagia as well as other uterine diseases in a minimally invasive way and eventually to minimize postoperative complications.
The present invention uses the optically diffusing fiber capable of emitting light in a plurality of directions to apply to photothermal treatment or photodynamic therapy through an insertion into an inner tissue of human body. Additionally, the optically diffusing fiber may be used for treating thyroid cancers, breast cancers, prostate cancers, kidney cancers, bladder cancers, brain tumor, inner uterine wall, localized liver cancers, skin cancers, cancer tissue, coagulation of inner tissue, removal of fat, etc.
Additionally, according to hybrid optical medical equipment for both diagnosis and treatment of tubular human tissue according to the present invention, acquisition of OCT images for tubular body tissue such as trachea, blood vessel and ureter, and induction of photothermal treatment of body tissue by laser may be integrally performed through a single probe, thereby increasing efficiency of lesion diagnosis of tubular body tissue and induction of treatment. Also, the OCT image for the body tissue may be monitored in real time before and after performing the induction of photothermal treatment of body tissue, thereby efficiently performing diagnosis for lesion tissue and induction of treatment while minimizing damage on body tissue. Especially, diagnosis for every respiratory disease such as asthma and an induction of treatment may be promoted.
Also, the catheter-based laser treatment device according to the present invention has effects of preventing tracheal stricture from being recurred after surgery, and minimizing complications such as inflammation, injection, etc. which may be occurred during recovery.
According to the present invention, the use of various balloon catheters with geometric shapes may minimize hemorrhage by a blood vessel before or during treatment by using expansion of the balloon catheter, and induce vascular stricture without contraction of the balloon catheter.
The present disclosure is described with reference to the above embodiments. It should be appreciated by those skilled in the art that various changes and modifications may be made to the embodiments without departing from the scope of the present disclosure. Thus, the described embodiments set forth above are intended solely for explanatory purposes, not for limiting the present disclosure. The scope of the present disclosure is defined by the claims below. It should be appreciated that the present disclosure is not limited to the above embodiments, and all changes and/or equivalents thereto also belong to the scope of the present disclosure.
| Number | Date | Country | Kind |
|---|---|---|---|
| 10-2014-0046881 | Apr 2014 | KR | national |
| 10-2014-0114243 | Aug 2014 | KR | national |
| 10-2014-0121830 | Sep 2014 | KR | national |
| 10-2014-0157934 | Nov 2014 | KR | national |
This application is the national stage for International Patent Cooperation Treaty Application PCT/KR2014/012022, filed Dec. 8, 2014, which claims priority from Korean Patent Application No. 10-2014-0046881, filed on Apr. 18, 2014, in the Korean Intellectual Property Office; Korean Patent Application No. 10-2014-0114243, filed on Aug. 29, 2014, in the Korean Intellectual Property Office; Korean Patent Application No. 10-2014-0121830, filed on Sep. 15, 2014, in the Korean Intellectual Property Office; and Korean Patent Application No. 10-2014-0157934, filed on Nov. 13, 2014, also in the Korean Intellectual Property Office. The entire contents of said applications are incorporated herein by reference for all purposes.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/KR2014/012022 | 12/8/2014 | WO | 00 |
