Scanning optical fiber, light treatment device, light treatment system, and light treatment method

Abstract

A scanning optical fiber (1) is provided with an optical fiber (3) and a protruding member (5) that is provided in a tip region (3c) of the optical fiber (3) and has an outer diameter larger than the outer diameter of the optical fiber (3). The protruding member (5) receives a flow of a fluid (C) in the longitudinal direction of the optical fiber (3) toward the tip (3a) of the optical fiber (3) and generates a force in the radial direction of the optical fiber (3).

Description

Technical Field

[0001] This invention relates to a scanning optical fiber, a phototherapy device, a phototherapy system, and a phototherapy method. Background Technology

[0002] Previously, there were known stone fragmentation techniques that used laser beams to break up stones formed in the kidneys, etc. (see, for example, Non-Patent Document 1 and Patent Document 1). In order to efficiently break up stones, it is preferable to scan and irradiate the stones with a laser beam.

[0003] Non-Patent Document 1 and Patent Document 1 disclose vibration mechanisms for vibrating the tip of an optical fiber to enable scanning with a laser beam. The vibration mechanism in Non-Patent Document 1 uses a magnetic bead fixed to the optical fiber and a solenoid near the fiber, vibrating the tip of the fiber using magnetic force. The vibration mechanism in Patent Document 1 uses a plate-shaped actuating member disposed near the optical fiber, vibrating the tip of the fiber by the contraction of bubbles generated at the tip of the fiber by the laser beam.

[0004] Existing technical documents

[0005] Non-patent literature

[0006] Non-Patent Literature 1: Layton A. Hall and 2 others, “Thulium fiber laser stonedusting using an automated, vibrating optical fiber,” Proceedings SPIE 10852, Therapeutics and Diagnostics in Urology 2019, February 26, 2019

[0007] Patent documents

[0008] Patent Document 1: International Publication No. 2022 / 190259 Summary of the Invention

[0009] The problem the invention aims to solve

[0010] The vibration mechanism in Non-Patent Document 1 requires a driving power source, which inevitably leads to large-scale operation.

[0011] In order to control the timing of bubble formation, the vibration mechanism in Patent Document 1 requires specific conditions for the laser beam. However, it is desirable that the laser beam conditions, such as the pulse waveform and frequency, can be varied according to the size and type of the stone.

[0012] The present invention was made in view of the above circumstances, and its object is to provide a scanning optical fiber, a phototherapy device, a phototherapy system, and a phototherapy method that can be miniaturized and whose laser beam conditions can be arbitrarily set.

[0013] Solution for solving the problem

[0014] One aspect of the present invention is a scanning optical fiber comprising: an optical fiber; and a protruding member disposed in the front end region of the optical fiber, having an outer diameter larger than the outer diameter of the optical fiber, wherein the protruding member is subjected to a radial force on the optical fiber by the flow of fluid toward the front end of the optical fiber in the long side direction of the optical fiber.

[0015] Another aspect of the invention is a phototherapy device comprising: a medical tube having a channel; an optical fiber inserted into the channel; and a protruding member disposed at the front end region of the optical fiber, having an outer diameter larger than the outer diameter of the optical fiber, wherein the protruding member is subjected to a radial force on the optical fiber by the flow of fluid toward the front end of the optical fiber in the long side direction of the optical fiber.

[0016] Another aspect of the invention is a phototherapy system comprising: a medical tube having a channel; an optical fiber inserted into the channel; a protruding member disposed at the front end region of the optical fiber having an outer diameter larger than the outer diameter of the optical fiber; a fluid supply source supplying fluid to the channel; and a laser source providing a laser beam to the optical fiber, wherein the protruding member generates a radial force on the optical fiber due to the flow of fluid toward the front end of the optical fiber in the long side direction of the optical fiber.

[0017] Another aspect of the invention is a phototherapy method comprising: irradiating a target with a laser beam from a front end of an optical fiber; and vibrating the front end of the optical fiber, wherein the vibration includes generating a flow of fluid toward the front end of the optical fiber in the direction of the long side of the optical fiber, and a protruding member disposed in the front end region of the optical fiber is subjected to the flow of the fluid to generate a radial force on the optical fiber.

[0018] Invention Effects

[0019] According to the present invention, it achieves the effect of enabling miniaturization and allowing the laser beam conditions to be set arbitrarily. Attached Figure Description

[0020] Figure 1 This is an overall structural diagram of a phototherapy system according to one embodiment of the present invention.

[0021] Figure 2 This is a partial side view of a scanning optical fiber according to one embodiment.

[0022] Figure 3A This is a diagram illustrating an example of the conditions for a laser beam.

[0023] Figure 3BThis is another diagram illustrating the conditions of a laser beam.

[0024] Figure 3C This is a diagram showing the conditions of a laser beam in the case of a conventional scanning fiber that vibrates by the contraction of bubbles.

[0025] Figure 4 This is a flowchart of a phototherapy method according to one embodiment of the present invention.

[0026] Figure 5A This is a diagram showing a scanning optical fiber used in the treatment of kidney stones.

[0027] Figure 5B This is a diagram showing a previous scanning fiber optic method used in the treatment of kidney stones.

[0028] Figure 6 It is a cross-sectional view of the wing-shaped functional component.

[0029] Figure 7 This is an explanation Figure 6 The diagram shows the function of the components.

[0030] Figure 8 It is a partial side view of a scanning optical fiber with a columnar or rotating body as its functional component.

[0031] Figure 9A It is shown Figure 8 A diagram of an example of the cross-section of a component.

[0032] Figure 9B It is shown Figure 8 Another example of the cross-section of the component is shown in the figure.

[0033] Figure 9C It is shown Figure 8 Another example of the cross-section of the component is shown in the figure.

[0034] Figure 9D It is shown Figure 8 Another example of the cross-section of the component is shown in the figure.

[0035] Figure 9E It is shown Figure 8 Another example of the cross-section of the component is shown in the figure.

[0036] Figure 9F It is shown Figure 8 Another example of the cross-section of the component is shown in the figure.

[0037] Figure 9G It is shown Figure 8 Another example of the cross-section of the component is shown in the figure. Detailed Implementation

[0038] Hereinafter, with reference to the accompanying drawings, a scanning optical fiber, a phototherapy device, a phototherapy system, and a phototherapy method according to one embodiment of the present invention will be described.

[0039] like Figure 1 As shown, the phototherapy system 100 of this embodiment is a stone-breaking system that uses a laser beam L to break up stones, which are the treatment target A. The phototherapy system 100 includes a phototherapy device 10, a laser light source 20, a fluid supply source 30, and a control unit 40.

[0040] The phototherapy device 10 is equipped with a scanning optical fiber 1 and a medical tube 2.

[0041] The medical tube 2 is an endoscope with a long, flexible insertion portion 2a. Images of the body B obtained by the endoscope 2 can also be displayed on the display unit 50. The endoscope 2 has a channel 2b that extends through the insertion portion 2a along its long side, and the channel 2b has an outlet 2c that opens at the front end face of the endoscope 2. The channel 2b of the endoscope 2 serves as a channel for the irrigation fluid C and the optical fiber 3, and also as a passage for inserting other treatment instruments.

[0042] The scanning optical fiber 1 includes an optical fiber 3, an optical fiber holding part 4, and an active member (protruding member) 5.

[0043] The optical fiber 3 has a front end 3a for emitting a laser beam L and a base end 3b connected to the laser source 20. The optical fiber 3 has an outer diameter smaller than the inner diameter of the channel 2b, so that it can be inserted into the channel 2b.

[0044] The fiber holding part 4 holds a portion of the fiber 3 at intervals along its long side starting from the front end 3a, thereby fixing the portion of the fiber 3 so that the fiber 3 will not move radially within the channel 2b. For example, the fiber holding part 4 is a cylindrical component mounted on the side of a portion of the fiber 3, having an outer diameter slightly smaller than the inner diameter of the channel 2b.

[0045] The cantilever-beam-shaped front end region 3c of the optical fiber 3, protruding from the front end face of the holding part 4, is a vibration region that vibrates radially. The vibration region 3c vibrates radially with the portion held by the holding part 4 as the fulcrum, thereby causing the laser beam L emitted from the front end 3a to scan.

[0046] In addition, the optical fiber holding part 4 has a shape that allows the perfusion fluid C to pass through along the long side direction of the optical fiber holding part 4, for example, it has a flow path extending along the long side direction.

[0047] The actuating member 5 is fixed to a portion of the side of the vibration region 3c between the front end 3a and the optical fiber holding part 4. The front end of the actuating member 5 is positioned at a distance from the front end 3a toward the base end, and the base end of the actuating member 5 is positioned at a distance from the front end of the optical fiber holding part 4 toward the front end.

[0048] The actuating member 5 has an outer diameter larger than that of the optical fiber 3 and protrudes radially from the side of the optical fiber 3. The maximum outer diameter of the actuating member 5 is less than or equal to the inner diameter of the channel 2b, allowing the actuating member 5 to pass through the channel 2b together with the optical fiber 3. The outer diameter of the actuating member 5 refers to its dimension in the direction orthogonal to the long side axis 3d of the optical fiber 3. In one example, the inner diameter of the channel 2b is 1.2 mm, and the maximum outer diameter of the actuating member 5 is less than or equal to 1.2 mm.

[0049] like Figure 2 As shown, the perfusion fluid C flowing from the base end toward the front end within channel 2b forms a flow near outlet 2c toward the front end 3a, parallel or approximately parallel to the long side of the optical fiber 3. The actuating member 5 is positioned to block the flow of the perfusion fluid C, and is affected by the flow of the perfusion fluid C, generating a radial F (refer to...) in the optical fiber 3. Figure 7 and Figure 8 Specifically, the actuating member 5 deflects the flow direction of the irrigation fluid C radially, thereby generating a lift force F perpendicular to the flow direction of the irrigation fluid C. In the vibration region 3c, which flexes with the lift force F and experiences radial displacement, a radial restoring force G is generated to restore the fluid to a straight shape (see reference). Figure 7 The action member 5 generates a lift force F such that the direction of the resultant force of the lift force F and the restoring force G is periodically reversed, thereby causing the vibration region 3c to vibrate. The specific structure of the action member 5 will be described in detail later.

[0050] To prevent interference between the actuating member 5 and the inner surface of the channel 2b, it is preferable that at least a portion of the actuating member 5 is disposed outside the outlet 2c, more preferably that the entire actuating member 5 is disposed outside the outlet 2c. The preferred protruding length of the optical fiber 3 from the tip of the endoscope 2 to the tip 3a is 2mm to 20mm. Therefore, the base of the actuating member 5 is preferably disposed at a position 2mm to 20mm from the tip 3a.

[0051] The laser source 20 is, for example, a laser oscillator, optically connected to the base end 3b of the optical fiber 3. In response to the operation of the foot switch 20a, the laser source 20 outputs a pulsed laser beam L for treating the object A. The laser beam L is, for example, infrared light.

[0052] The fluid supply source 30 is fluidly connected to the base of the channel 2b to supply an irrigation fluid C, such as physiological saline, to the channel 2b. For example, the fluid supply source 30 has a bag for containing the irrigation fluid C and a tube connecting the bag to the channel 2b, supplying the irrigation fluid C to the channel 2b in a manner that allows it to drip naturally from the bag.

[0053] In order for the actuating member 5 to stably generate lift F, it is preferable that the perfusion fluid C forms a uniform flow near the outlet 2c. Therefore, the fluid supply source 30 supplies the perfusion fluid C at a constant flow rate (e.g., 20 ml / min).

[0054] The magnitude of the lift F generated by the actuating component 5 depends on the flow rate of the irrigation fluid C. In order to adjust the magnitude of the lift F, the fluid supply source 30 can also be a pump capable of changing the flow rate of the irrigation fluid C, for example, it can be a pump with a flow rate control capability.

[0055] The fluid supply source 30 can also synchronize with the vibration of the optical fiber 3 to change the flow rate of the perfusion fluid C over time.

[0056] The control unit 40 controls the conditions for the laser beam L output by the laser source 20. Figure 3A and Figure 3B An example of a laser beam L is shown. Conditions include, for example, the pulse waveform, the number of pulses n in a pulse group, the repetition frequency f, and the interval T between pulse groups.

[0057] Next, a phototherapy method using scanning fiber optic 1, phototherapy device 10, and phototherapy system 100 will be described.

[0058] like Figure 4 As shown, the phototherapy method includes: step S1, placing the endoscope 2 inside body B; step S2, preparing an optical fiber 3 with an active component 5 installed; step S3, inserting the optical fiber 3 with the active component 5 installed into the channel 2b of the endoscope 2; step S4, irradiating the object A with a laser beam L; and step S5, causing the tip 3a of the optical fiber 3 to vibrate.

[0059] The operator, for example, inserts an endoscope 2 into the kidney through the urethra (step S1).

[0060] Next, the operator, for example, installs the retaining part 4 and the actuating member 5 on the side of the optical fiber 3 by passing the optical fiber 3 through the through holes respectively provided in the retaining part 4 and the actuating member 5 (step S2). Alternatively, the operator may be provided with an optical fiber 3 pre-installed with the retaining part 4 and the actuating member 5.

[0061] Next, the operator inserts the optical fiber 3, which is equipped with the retaining part 4 and the actuating member 5, into the channel 2b, and positions the front end 3a of the optical fiber 3 and the actuating member 5 from the outlet 2c to the outside of the channel 2b, and positions the retaining part 4 inside the channel 2b (step S3).

[0062] Next, the operator steps on foot switch 20a to start outputting laser beam L from laser source 20 (step S4). The laser beam L is irradiated from the front end 3a of optical fiber 3 onto object A to break up the stone in object A.

[0063] Step S5 is performed in parallel with step S4. In step S5, the operator supplies irrigation fluid C from fluid supply source 30 to channel 2b, thereby generating a flow of irrigation fluid C in the vicinity of vibration region 3c, towards the front end 3a, along the long side of vibration region 3c, near outlet 2c (step S5). This flow of irrigation fluid C collides with the actuating member 5, generating lift F, causing vibration region 3c to vibrate. As a result, laser beam L scans on stone A, irradiating a large area of ​​stone A with laser beam L. Therefore, the treatment efficiency using laser beam L, such as the fragmentation efficiency of stone A, can be improved.

[0064] In addition, in step S5, the perfusion fluid C improves the poor field of vision of endoscope 2 caused by the fragments of stone A, thereby obtaining a clear field of vision and suppressing the temperature rise in the kidney caused by the laser beam L.

[0065] In the treatment of kidney stone A, perfusion fluid C is supplied to the body B through channel 2b to improve visual field and inhibit renal elevation. According to this embodiment, the energy of the perfusion fluid C flow is converted by the action member 5 into radial lift F in the optical fiber 3, causing the optical fiber 3 to vibrate. That is, the flow of perfusion fluid C is used as the driving source for vibration. Therefore, a driving source such as a power supply is not required, enabling the realization of a small device 10 and system 100.

[0066] Furthermore, in cases where a vibration mechanism that generates an electromagnetic field is used, as in Non-Patent Document 1, the electromagnetic field may affect the quality of the endoscopic image. The scanning fiber optic 1 of this embodiment does not require an electromagnetic field, thus enabling the acquisition of excellent endoscopic images.

[0067] Furthermore, since the vibration of fiber 3 caused by the lift F is independent of the conditions of the laser beam L, the conditions of the laser beam can be arbitrarily set. Therefore, as... Figure 3A and Figure 3B As shown, a laser beam L that is appropriate to the size, type, and other conditions of object A can be used to further improve the treatment effect of object A.

[0068] As in Patent Document 1, when the front end 3a is vibrated by the contraction of a bubble formed by the laser beam L, specific conditions of the laser beam L are required. For example, ... Figure 3C As shown, the number of pulses n, the repetition frequency f, and the interval T are limited to a specified range. Therefore, it is difficult to adjust the conditions of the laser beam L according to the object A.

[0069] Furthermore, according to this embodiment, the actuating member 5 is positioned closer to the base end than the front end 3a, and the scanning optical fiber 1 does not have any structure near the front end 3a. Therefore, as Figure 5A As shown, it can prevent the scanning of the laser beam L from being hindered by interference between the active component 5 and the stone A phase.

[0070] As in Patent Document 1, when a plate-shaped action member 105 is provided to apply the contraction force of bubble E to the front end 3a, the scanning of the laser beam L may be hindered due to interference between the action member 105 and the stone A (see reference). Figure 5B ).

[0071] Next, a specific example of the functional component 5 will be explained. Figure 6 and Figure 7 The plate-shaped functional component 5 is shown. Figures 8 to 9G The functional component 5 of the column or rotating body is shown.

[0072] Figure 6 The actuating member 5 has a first surface 51 and a second surface 52 facing each other in the thickness direction, and is arranged obliquely relative to the long side axis 3d of the optical fiber 3. The cross-section of the actuating member 5 along the long side axis 3d is wing-shaped. The wing shape refers to the shape that generates lift by the pressure difference between the first surface 51 side and the second surface 52 side, and is generally a streamlined shape with a sharp trailing edge 5b and a smooth leading edge 5c. The chord 5a of the actuating member 5 is inclined at an angle θ relative to the long side axis 3d and at an elevation angle α with the flow direction of the perfusion fluid C. When the vibration region 3c is arranged in an initial position without deflection, the elevation angle α is equal to the angle θ.

[0073] The plate-shaped actuating member 5 can also have other cross-sectional shapes, provided that the lift F required for the vibration of the vibration region 3c can be obtained. For example, the actuating member 5 can also be a plate that is inclined relative to the long side axis 3d and deflects the flow of the irrigation fluid C. The plate actuating member 5 receives a reaction force from the flow by deflecting the flow of the irrigation fluid C, generating a lift F caused by the reaction force.

[0074] Figure 7 This explains the vibration of the vibration region 3c caused by the lift force F and the restoring force G of the optical fiber 3.

[0075] When the vibration region 3c is positioned in the initial position, the action member 5 generates lift F (t=t1) through the flow of the irrigation fluid C. In the initial position, the restoring force G of the vibration region 3c is zero, and the vibration region 3c flexes with the lift F and undergoes radial displacement.

[0076] The displacement of the vibration region 3c relative to its initial position generates a restoring force G that is directed in the opposite direction to the lift F. As the displacement increases, the restoring force G increases. Furthermore, as the displacement increases, the elevation angle α decreases, thereby decreasing the lift F. Therefore, the resultant force of the lift F and the restoring force G reverses direction, and the vibration region 3c subsequently undergoes a displacement in the opposite direction to its initial position (t=t2).

[0077] During the displacement in the opposite direction to the initial position, the lift force F increases, and the restoring force G decreases. Therefore, the direction of the resultant force reverses again.

[0078] When the vibration region 3c has undergone displacement in the opposite direction from its initial position, the orientation of the restoring force G is the same as that of the lift force F (t=t3). As the displacement increases, the restoring force G increases. Furthermore, as the displacement increases, the elevation angle α increases, thereby increasing the lift force F. Therefore, the vibration region 3c subsequently undergoes displacement toward its initial position.

[0079] In this way, the wing-shaped action member 5 always generates lift F in the same direction, and the magnitude of lift F varies with the angle of attack α. Furthermore, the direction of the restoring force G changes periodically. Therefore, the periodic reversal of the direction of the resultant force enables the vibration region 3c to vibrate.

[0080] The lift F generated by component 5 depends on the angle θ and the camber β. The camber β is the distance between the chord 5a and the centerline 5d. The angle θ and camber β are designed to achieve the vibration described above.

[0081] Figure 8 The action member 5 of the cylindrical or rotating body is symmetrical with respect to the plane containing the long side axis 3d, and a Karman vortex K is generated at the front end of the action member 5. The Karman vortex K is a series of multiple vortices, and the rotation directions of the vortices are alternately opposite. Therefore, the action member 5 alternately generates lift F1 and lift F2 in the opposite direction to lift F1, thereby causing the vibration region 3c to vibrate. In the case of the action member 5 of the cylindrical body, the front end 3a undergoes one-dimensional vibration in the radial direction. In the case of the action member 5 of the rotating body, the front end 3a undergoes two-dimensional vibration in the radial plane.

[0082] In order to be able to pass through the channel 2b, the maximum outer diameter of the actuating member 5 is less than or equal to the inner diameter of the channel 2b (e.g., 1.2 mm).

[0083] The column has a height orthogonal to the long side axis 3d and a pair of bases located on both sides of the long side axis 3d. Figures 9A to 9G Examples showing the shape of the base or a cross-section perpendicular to the height, where the height is in a direction orthogonal to the plane of the paper. For example... Figures 9A to 9GAs shown, the shape of the base or cross-section can also be circular, projectile-shaped, triangular, square, trapezoidal, rectangular with a short side along the direction of the long side axis 3d, or roughly T-shaped. The shape of the base and cross-section can be any shape that can generate the Karman vortex K, or it can be other polygons or other shapes that are linearly symmetrical with respect to the long side axis 3d.

[0084] A body of revolution is one that makes Figures 9A to 9G A three-dimensional solid formed by rotating a planar figure that is linearly symmetric about its long axis 3d around the long axis 3d, as shown, is symmetric about its long axis 3d. For example, the functional component 5 of the solid of revolution is a sphere ( Figure 9A As described above, the rotating body's working member 5 causes the front end 3a to vibrate in two dimensions, which is advantageous in that it can irradiate the laser beam L over a wider area.

[0085] The shape of the cross-section of a prism and a solid of revolution can also be... Figures 9A to 9G The shape of the planar graphic after being flipped in the left-right direction. That is, the direction of the flow of the irrigation fluid C relative to the action member 5 can be either from left to right (D1) or from right to left (D2).

[0086] As is well known, cylinders and rotating bodies generate Karman vortices when the Reynolds number is within a specified range, and the Reynolds number depends on the flow velocity and the size of the cylinder or rotating body. Therefore, the dimensions of the active component 5 are designed to generate Karman vortices at the desired flow velocity of the perfusion fluid C.

[0087] Regarding the action component 5 of the column, the vibration direction of the vibration region 3c depends on the height of the action component 5.

[0088] When describing the cylindrical member 5, if the height is sufficiently large (e.g., the height is larger than the diameter of the base), the direction of vibration is parallel to the base. Figure 9A (The vertical direction is shown in the image). On the other hand, as the height decreases, the shape of the active component 5 approaches that of a circular plate. When the height is sufficiently small (for example, about 1 / 10 of the diameter of the bottom surface), the vibration direction is in the height direction. Figure 9A (The direction perpendicular to the paper).

[0089] Thus, the smaller the height, the closer the actuating member 5 is to a plate shape, and the closer the vibration direction is to the height direction. Similarly, in the case of actuating members 5 with other bottom shapes, the vibration direction also depends on the height.

[0090] In the above embodiment, the medical tube is assumed to be an endoscope 2, but the medical tube can also be any length of medical device with a channel 2b, such as a catheter.

[0091] In the above embodiment, the fiber holding part 4 is installed on the side of the fiber 3, but it is also possible to replace it by setting the fiber holding part 4 on the inner surface of the channel 2b.

[0092] In the above embodiment, the scanning optical fiber 1 is inserted into the body B through the channel 2b of the medical tube. However, alternatively, the scanning optical fiber 1 can be inserted into the body B independently of the medical tube. In this case, the outer diameter of the actuating member 5 can also be larger than the inner diameter of the channel 2b. Furthermore, any means can be used to generate the flow of perfusion fluid C required to produce lift F around the vibration region 3c.

[0093] The embodiments and variations of the present invention have been described above, but the present invention is not limited thereto, and appropriate changes can be made without departing from the spirit of the present invention.

[0094] For example, the phototherapy device 10 and phototherapy system 100 are not limited to stone fragmentation, but can be applied to any treatment that irradiates light onto the subject A, and are particularly well-suited for treatments performed while simultaneously supplying liquid or gas. Depending on the type of treatment, the fluid supplied by the fluid supply source 30 to the channel 2b can also be appropriately selected. That is, the fluid supply source 30 can also supply other liquids or gases to the channel 2b.

[0095] In addition, the scanning fiber 1 can be used not only for treatment, but also for other applications that enable laser beam scanning.

[0096] Explanation of reference numerals in the attached figures

[0097] 1. Scanning fiber optic

[0098] 2. Endoscope (medical tube)

[0099] 3 optical fibers

[0100] 3c Vibration region (front end region)

[0101] 3D long axis

[0102] 5. Functional Components (Protruding Components)

[0103] 10. Phototherapy device

[0104] 20 Laser Sources

[0105] 30 Fluid supply source

[0106] 100 Light Therapy System

[0107] Object A

[0108] C. Irrigation fluid (fluid)

[0109] F, F1, F2 lift

[0110] L laser beam

Claims

1. A scanning optical fiber, comprising: Fiber optics; and A protruding member, disposed in the front end region of the optical fiber, has an outer diameter larger than the outer diameter of the optical fiber. in, The protruding member is subjected to a radial force on the optical fiber due to the flow of fluid toward the front end of the optical fiber along its long side.

2. The scanning optical fiber according to claim 1, wherein, The protruding member is a plate-shaped member that is inclined relative to the long axis of the optical fiber.

3. The scanning optical fiber according to claim 2, wherein, The protruding member has a wing-shaped cross-section.

4. The scanning optical fiber according to claim 1, wherein, The protruding component is a column or a body of revolution. The column has a height in a direction orthogonal to the long axis of the optical fiber and is symmetrical with respect to the plane containing the long axis. The rotating body is symmetrical about the long side axis.

5. The scanning optical fiber according to claim 4, wherein, The protruding member has a circular, polygonal, or projectile-shaped cross section that is linearly symmetrical with respect to the long side axis.

6. The scanning optical fiber according to claim 1, wherein, The protruding member has an outer diameter below the inner diameter of the channel for insertion of the scanning optical fiber into the medical tube.

7. A phototherapy device, comprising: Medical tubes, which have access channels; An optical fiber, which is inserted into the channel; and A protruding member, disposed in the front end region of the optical fiber, has an outer diameter larger than the outer diameter of the optical fiber. in, The protruding member is subjected to a radial force on the optical fiber due to the flow of fluid toward the front end of the optical fiber along its long side.

8. The phototherapy device according to claim 7, wherein, The outer diameter of the protruding member is less than or equal to the inner diameter of the channel.

9. The phototherapy device according to claim 7, wherein, The medical tube is an endoscope.

10. A phototherapy system, comprising: Medical tubes, which have access channels; An optical fiber is inserted into the channel; A protruding member is disposed in the front end region of the optical fiber and has an outer diameter larger than that of the optical fiber. A fluid supply source that supplies fluid to the channel; as well as A laser source supplies a laser beam to the optical fiber. The protruding member is subjected to a radial force on the optical fiber by the flow of fluid toward the front end of the optical fiber along its long side.

11. The phototherapy system according to claim 10, wherein, The protruding member is a plate-shaped member that is inclined relative to the long axis of the optical fiber.

12. The phototherapy system according to claim 11, wherein, The protruding member has a wing-shaped cross-section.

13. The phototherapy system according to claim 10, wherein, The protruding component is a column or a body of revolution. The column has a height in a direction orthogonal to the long axis of the optical fiber and is symmetrical with respect to the plane containing the long axis. The rotating body is symmetrical about the long side axis.

14. The phototherapy system according to claim 13, wherein, The protruding member has a circular, polygonal, or projectile-shaped cross section that is linearly symmetrical with respect to the long side axis.

15. The phototherapy system according to claim 10, wherein, The protruding member has an outer diameter below the inner diameter of the channel for the medical tube into which the optical fiber is inserted.

16. A phototherapy method, comprising: A laser beam is directed from the tip of the optical fiber toward the object. as well as Vibrate the tip of the optical fiber. The vibration includes generating a flow of fluid toward the front end of the optical fiber along its long side, and a protruding member disposed in the front end region of the optical fiber is subjected to the flow of the fluid to generate a radial force on the optical fiber.

17. The phototherapy method according to claim 16, wherein, The protruding member is a plate-shaped member that is inclined relative to the long axis of the optical fiber.

18. The phototherapy method according to claim 17, wherein, The protruding member has a wing-shaped cross-section.

19. The phototherapy method according to claim 16, wherein, The protruding component is a column or a body of revolution. The column has a height in a direction orthogonal to the long axis of the optical fiber and is symmetrical with respect to the plane containing the long axis. The rotating body is symmetrical about the long side axis.

20. The phototherapy method according to claim 19, wherein, The protruding member has a circular, polygonal, or projectile-shaped cross section that is linearly symmetrical with respect to the long side axis.

21. The phototherapy method according to claim 16, wherein, The protruding member has an outer diameter below the inner diameter of the channel for the medical tube into which the optical fiber is inserted.

Images