JP4997364B2 - Light irradiation probe - Google Patents

Description

  The present invention relates to a light irradiation probe used for examining specific cells, diseased cells, tumors, affected areas, and the like, and a fundus oculi observation device, a fundus surgery device, and an endoscope using the light irradiation probe.

  Fluorescence diagnostic methods are well known as diagnostic methods for cancer and diseased tissue in the medical field. Fluorescence diagnostic methods are used to mark specific cells or diseased cells with fluorescent drugs, irradiate these cells with light that matches the absorption spectrum of the fluorescent drugs, and detect the fluorescence emitted from the fluorescent drugs. A diagnostic method for detecting diseased cells.

  In order to enhance the detection capability of the diagnostic method, it is necessary to increase the intensity of light (hereinafter referred to as external irradiation light or irradiation light) that is applied to the fluorescent agent from the outside. This is because by setting the intensity high, the fluorescence becomes strong and the marked specific cells and diseased cells can be easily detected.

  As a surgical method using external irradiation light, a light irradiation surgical method called light assist is well known. This surgical method is a method in which, for example, light-absorbing nanoshell particles are injected into tumor affected cells, light is irradiated from the outside, and the tumor is thermally destroyed by photothermal conversion of the nanoshell particles. Furthermore, local pharmacological treatment using photoreactive drug technology (photoreactive drug excitation method) is also well known.

  Also in these surgical methods, it is necessary to set the intensity of external irradiation light to be high in order to increase the effect of thermal destruction and the generation efficiency of the photoderivative reactive agent. There are the following two requirements that must be taken into consideration when increasing the intensity of the external irradiation light.

  First, even if a light irradiation device is brought close to a specific cell, diseased cell, tumor, or affected part and external irradiation light is irradiated, the visual field for monitoring and observing the irradiation state is not hindered. Second, the irradiation range of the external irradiation light is appropriate so that the visual field for monitoring and observation is not hindered.

  The reason for the first requirement is that externally irradiated light illuminates the affected area through body fluid or Ringer's solution, but in the optical path, scattering occurs due to fine particles in the body fluid or Ringer's solution, and this appears as flare, which can be detected, monitored, This is because observation becomes difficult.

  The reason for the second requirement is that when the irradiation range of the external irradiation light is narrow, the cells that are marked with the fluorescent agent emit fluorescence only with the cells that are actually irradiated with the external irradiation light. This is because the purpose of detecting all specific cells, diseased cells, tumors, and affected areas cannot be achieved.

  As means for solving these problems, there is a method in which an optical fiber is used for the light irradiation device, and light is irradiated by bringing the optical fiber close to a specific cell, a diseased cell, a tumor, or an affected part. In this way, even if light is irradiated in front of the optical monitoring / observing apparatus, the optical fiber is small, and it is unlikely to become an obstacle in the monitoring field of view. Further, since the optical fiber irradiates light close to the irradiation target, light scattering in the medium in between is small. This satisfies the requirement described in the first requirement that the visual field for monitoring and observation is not obstructed even if the light irradiation device is brought close to the device.

  However, propagating light whose wavefront is held in a plane perpendicular to the propagation optical axis inside the core of the optical fiber propagates in free space outside the optical fiber, so that the light spreads, and the wavefront is flat in the plane. Disappear. This divergence angle is about 5 degrees at most for an optical fiber, and the irradiation range of the irradiation light from the end of the optical fiber is as narrow as several degrees, so the monitoring / observation range becomes small. If the end portion of the optical fiber is moved away from the position of the monitoring / observing device in order to spread the irradiation light, scattering occurs and a part of the irradiation light is shielded by the monitoring / observing device. Therefore, the range of monitoring and observation is hindered. In order to solve this, it is necessary to increase the spatial extent of the external irradiation light from the end face of the optical fiber.

  On the other hand, conventionally, the end of the optical fiber is processed to have a parabolic cross section and shaped into a bullet shape, thereby increasing the spatial spread of the external irradiation light. A partial structure has been devised (see, for example, Patent Document 1).

Japanese Unexamined Patent Publication No. 2003-111789 (page 6-7, FIG. 2)

  FIG. 50 (a) shows a partial side sectional view of a light irradiation probe provided with an optical fiber including such an end structure, and FIG. 50 (b) shows a front view from the corresponding end. If the end portion of the light irradiation probe 100 has a bullet shape, the external irradiation light emitted from the end portion 101 of the optical fiber is scattered and irradiated over a wide range.

  The shape of the end portion 101 of the optical fiber is not particularly limited, and the end portion of the main body portion 102 only needs to have a parabolic cross section in the direction along the longitudinal direction.

  However, widening the irradiation range of the external irradiation light only by scattering at the end portion 101 of the optical fiber also causes light backscattering 103 as shown in FIG. Due to this backscattering 103, the backscattered light hits the fine particles in the body fluid or Ringer's solution located behind the end portion 101 of the optical fiber, and enters the field of view of the monitoring / observation device located behind the end portion of the optical fiber. Flare occurs. As a result, the monitoring / observation field of view is not an image with a good so-called “missing”, and it is difficult to confirm fluorescence.

  Further, in the light irradiation probe 100 of FIG. 50, since the end portion 101 of the optical fiber is rounded, the wave front of the propagation light is bent at the end portion 101 of the optical fiber, and the propagation light is free due to the condensing action of the rounding processing. There was also a problem that the desired spatial extent could not be obtained due to condensing light after exiting into space.

  The present invention has been made in view of the above problems, and its purpose is to provide a light irradiation probe that expands the spatial extent of external irradiation light, and a fundus oculi observation device, a fundus surgery device using the light irradiation probe, It is to provide an endoscope.

The invention according to claim 1 of the present invention includes a light propagation part and a light emission part in the optical fiber axial direction, and the refractive index spatial distribution of the light emission part is different from the refractive index spatial distribution of the light propagation part. The optical propagation part is an optical fiber having a configuration in which the core and a clad having a refractive index lower than the refractive index of the core surround the periphery of the core, and the light emitting part has the same refractive index as that of the core. In addition, Er, Nd, Ho, Tm, Pr, Sm, Dy, Yb, and Ti are doped at the tip of the lens portion of the light emitting portion, and the tip is the core. The optical radiation portion is provided on the end side of the optical fiber, and converts the wavefront of light from a plane to a curved surface in the optical fiber axis direction, The tip is further converted into a curved surface and irradiated with light to provide a fundus observation device. It is a light irradiation probe characterized by being used for a placement, a fundus operation apparatus, or an endoscope .

Furthermore, the invention according to claim 2 is the light irradiation probe according to claim 1 ,
One or a plurality of planes are formed at the tip of the light emitting part at an angle less than 90 degrees non-parallel to the axial direction of the light propagating part. It is.

Furthermore, the invention according to claim 3 is the light irradiation probe according to claim 1 ,
The light emitting probe is characterized in that the tip of the light emitting portion is formed in a conical shape.

  According to the light irradiation probe of the present invention, the propagation angle of the propagation light is increased before the propagation light reaches the lens portion, which is a tip portion having a parabolic cross section, to widen the irradiation range of the external irradiation light. It becomes possible to suppress the backscattering of light. Therefore, in the apparatus to which this light irradiation probe is applied, it is possible to prevent the occurrence of flare due to the fine particles in the body fluid or Ringer's solution located behind the end of the optical fiber. This makes it possible to provide an apparatus that can obtain an image with a so-called “missing”.

  Furthermore, according to the light irradiation probe of the present invention, a wide irradiation range of the external irradiation light can be secured, so that it becomes easy to find a cell / tumor / affected area marked with a fluorescent agent.

Moreover, according to the light irradiation probe of Claim 2 or 3 of this invention, since the front-end | tip part of the light emission part which is a probe front-end | tip is shape | molded in sharp shape in addition to each said effect, When the light irradiation probe is inserted, a simple laceration is given to the surface of the eyeball, and the healing of the eyeball after the light irradiation probe is removed can be accelerated.

<First Embodiment>
The first embodiment of the present invention will be described below with reference to FIGS. FIG. 1 schematically shows a first embodiment of a light irradiation probe 1 according to the present invention. 2 is a cross-sectional view taken along the plane AA of FIG. 1, and FIG. 3 shows light propagation and radiation paths in the light irradiation probe 1 of the present embodiment.

  As shown in FIG. 1, the light irradiation probe 1 includes an optical fiber 2 that is a light propagation portion and a cannula 4 that is attached to the outer peripheral surface of the optical fiber 2. 5a is integrated with the optical fiber 2. Furthermore, a tip portion having a parabolic cross section is formed at the tip of the light emitting portion 5a by grinding and polishing. The tip portion having a parabolic cross section is defined as a lens portion 3. The broken line and the solid line shown in the optical fiber of FIG. 1 or 2 represent the boundary between the refractive indexes of the core 2a and the clad 2b.

The optical fiber 2 has a refractive index spatial distribution constituted by a core 2a and a clad 2b having a refractive index lower than that of the core 2a surrounding the core 2a. One light emitting portion 5a has the same refractive index spatial distribution as the refractive index of the core 2a. The region of the core 2a is gradually enlarged toward the outer peripheral surface of the optical fiber 2 as it approaches the end of the optical fiber 2, and is formed over the entire diameter of the cladding 2b before reaching the lens unit 3. The Thereby, a uniform refractive index space distribution of the light emitting portion 5a is formed.

  Next, the propagation and emission of light in the light irradiation probe 1 will be described with reference to FIG. As shown in FIG. 3, light is incident from the other end (not shown) of the optical fiber 2 and propagates through the optical fiber 2 toward the lens unit 3 side. The propagating light propagating through the optical fiber 2 is held in the propagation mode, and its wavefront is held perpendicularly and parallel to the axis of the core 2a.

Next, when light propagates from the optical fiber 2 to the light radiating portion 5a, the refractive index of the core 2a gradually spreads due to the change in the refractive index spatial distribution, and the light radiating portion 5a has almost the same refractive index. Thus, the wavefront is gradually converted from a flat surface to a curved surface. The mode of the propagating light is converted from the propagating mode to the radiation mode. Further, the propagating light incident on the lens unit 3 is emitted from the lens unit 3 to the outside of the probe 1 as external radiation light. Since the mode of the propagating light is converted into the radiation mode inside the light emitting unit 5a, the condensing action in the lens unit 3 is reduced, and the light propagation in the free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

  A hermetic seal 6 couples between the outer peripheral surface of the optical fiber 2 and the inner peripheral surface of the cannula 4. The hermetic seal 6 is formed by, for example, plating or vapor-depositing one or more of Ni, Pd, Cu, Al, Au or the like on the surface of the optical fiber 2 and then press-fitting the cannula 4 into the outer peripheral surface of the optical fiber 2. By doing. Alternatively, the hermetic seal 6 may be performed with an adhesive. As a result, it is possible to prevent invasion or leaving of germs between the inner peripheral surface of the cannula 4 and the outer peripheral surface of the optical fiber 2. The cannula 4 is attached so as to extend to the outer peripheral surface of the light emitting portion 5a, and a hermetic seal 6 is applied between either the outer peripheral surface of the optical fiber 2 or the outer peripheral surface of the light emitting portion 5a and the inner peripheral surface of the cannula 4. You may change to

  The light emitting part 5a is manufactured by immersing the tip of the optical fiber corresponding to the length of the light emitting part 5a in the axial direction of the optical fiber 2 in molten benzoic acid, and refraction of a clad (not shown) of the light emitting part 5a by proton exchange. This is done by raising the index to the refractive index of the core 2a.

  As another manufacturing method, MgO may be doped at the end of the optical fiber to perform proton exchange. As the doping method, after the ion implantation, the end of the optical fiber is annealed, the vapor of the doping material, or the vapor is exposed to a plasma atmosphere, Er, Nd, Ho, Tm, Pr, Sm There is a method of immersing the tip portion of the optical fiber 2 in a low-temperature molten glass pool in which a doping material such as Dy, Yb, or Ti is melted.

  Through the manufacturing method as described above, the light emitting portion 5 a is integrally formed at the end of the optical fiber 2 in parallel with the axial direction of the optical fiber 2.

<Second Embodiment>
Next, a second embodiment of the present invention will be described with reference to FIGS. FIG. 4 schematically shows a second embodiment of the light irradiation probe 7 according to the present invention. FIG. 5 is a cross-sectional view taken along the plane BB in FIG. 4, and FIG. 6 shows light propagation and radiation paths in the light irradiation probe 7 of the present embodiment. In addition, the same number is attached | subjected to the same location as 1st Embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

The second embodiment is different from the first embodiment in that the refractive index space distribution of the light emitting portion 5a ′ is formed to be the same as and uniform with the refractive index of the core 2a, and then the light emitting portion. The point is that the refractive index of the tip 3a on the lens unit 3 side inside 5a ′ is set higher than the refractive index of the core 2a.

A method for manufacturing such a light emitting portion 5a ′ will be described. Since the refractive index spatial distribution of the light emitting portion 5a ′ is the same as the refractive index of the core 2a shown in FIG. . Once the light emitting portion 5a ′ having the same refractive index spatial distribution as the core 2a is formed, then the tip 3a is doped with Er, Nd, Ho, Tm, Pr, Sm, Dy as a doping material. , Yb, Ti, etc. are doped so that only the refractive index of the tip 3a is higher than the refractive index of the core 2a. As the doping method, after the ion implantation, the end of the optical fiber is annealed, or the vapor of the doping material, or the vapor is exposed to a plasma atmosphere, or the molten low temperature molten glass pool in which the doping material is melted is used. There is a method of immersing the tip portion of the optical fiber 2.

Next, the propagation and emission of light in the light irradiation probe 7 will be described with reference to FIG. As shown in FIG. 6, the light propagating from the optical fiber 2 to the light radiating portion 5a ′ has its wavefront gradually changed from a flat surface to a curved surface due to a change in the refractive index spatial distribution, and its mode is radiated from the propagation mode. Converted to mode. Further, the wavefront is further converted into a curved surface by the refractive index of the tip 3a, and the propagating light enters the lens unit 3 and is emitted from the lens unit 3 to the outside of the probe 7 as external irradiation light. Therefore, since the divergence of the propagation light inside the light emitting portion 5a ′ is further expanded compared to the first embodiment, the irradiation range of the external irradiation light is further expanded as compared with the first embodiment. It becomes possible to do.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Third Embodiment>
Next, a third embodiment of the present invention will be described with reference to FIGS. FIG. 7 schematically shows a third embodiment of the light irradiation probe 8 according to the present invention. FIG. 8 is a cross-sectional view taken along the plane CC of FIG. 7, and FIG. 9 shows light propagation and radiation paths in the light irradiation probe 8 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

The third embodiment differs from the above embodiments in that the region of the core 2a in the axial direction of the optical fiber 2 is terminated inside the optical fiber 2, and the light emitting portion 5b is provided at the end of the optical fiber 2. However, it is integrally formed parallel to the axial direction of the optical fiber 2, and the refractive index spatial distribution of the light emitting portion 5b is the same as the refractive index of the cladding 2b and is formed uniformly.

A method of manufacturing such an optical fiber 2 will be described with reference to FIG. First, the end of the optical fiber is melted by heating to form water droplets by surface tension. As a result, the end portion of the optical fiber has the same refractive index spatial distribution as the refractive index of the cladding 2b. Next, the lens portion 3 is formed by grinding and polishing the end portion of the optical fiber in the form of water droplets up to the one-dot chain line in the figure, and the light emitting portion 5b is moved to the end portion side of the optical fiber 2. Formed to have.

  Next, the propagation and emission of light in the light irradiation probe 8 will be described with reference to FIG. As shown in FIG. 9, the light propagating from the optical fiber 2 to the light radiating portion 5b is converted from the propagation mode to the radiation mode by the end of the core 2a region, and the wavefront gradually changes from the plane. Converted to a curved surface. Further, the propagating light incident on the lens unit 3 is emitted from the lens unit 3 to the outside of the probe 8 as external radiation light. Since the mode of the propagating light is converted into the radiation mode inside the light emitting unit 5b, the condensing action in the lens unit 3 is reduced, and the light propagation in the free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Fourth embodiment>
Next, a fourth embodiment of the present invention will be described with reference to FIGS. FIG. 11 schematically shows a fourth embodiment of the light irradiation probe 9 according to the present invention. 12 is a cross-sectional view taken along the line D-D in FIG. 11, and FIG. 13 shows light propagation and radiation paths in the light irradiation probe 9 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The fourth embodiment is different from the above-described embodiments, particularly the third embodiment, in that the refractive index (refractive index spatial distribution) of the light emitting portion 5b ′ is the same as the refractive index of the cladding 2b and This is because the refractive index of the tip portion 3b on the lens unit 3 side inside the light emitting portion 5b ′ is set higher than the refractive index of the clad 2b after being formed uniformly.

A method for manufacturing such a light emitting portion 5b ′ will be described. Since the refractive index spatial distribution of the light emitting portion 5b ′ is the same as the refractive index of the cladding 2b shown in FIG. . Once the light emitting part 5b ′ having the same refractive index spatial distribution as the clad 2b is formed, Er, Nd, Ho, Tm, Pr, Sm, Dy as a doping material is then applied to the tip part 3b. , Yb, Ti, etc. are doped so that only the refractive index of the tip 3b is higher than the refractive index of the cladding 2b. As the doping method, after the ion implantation, the end of the optical fiber is annealed, or the vapor of the doping material, or the vapor is exposed to a plasma atmosphere, or the molten low temperature molten glass pool in which the doping material is melted is used. There is a method of immersing the end of the optical fiber.

Next, the propagation and emission of light in the light irradiation probe 9 will be described with reference to FIG. As shown in FIG. 13, the light propagating from the optical fiber 2 to the light radiating portion 5b ′ has its wavefront gradually changed from a flat surface to a curved surface due to a change in the refractive index spatial distribution, and the mode is radiated from the propagation mode. Converted to mode. Furthermore, the wavefront is further converted into a curved surface by the refractive index of the tip portion 3b, and the propagating light enters the lens unit 3 and is emitted from the lens unit 3 to the outside of the probe 9 as external radiation light. Therefore, since the divergence of the propagation light inside the light emitting portion 5b ′ is further expanded as compared with the third embodiment, the irradiation range of the external irradiation light is further expanded as compared with the third embodiment. It becomes possible to do.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Fifth embodiment>
Next, a fifth embodiment of the present invention will be described with reference to FIGS. FIG. 14 schematically shows a fifth embodiment of the light irradiation probe 10 according to the present invention. FIG. 15 is a cross-sectional view taken along the plane EE of FIG. 14, and FIG. 16 shows light propagation and radiation paths in the light irradiation probe 10 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The fifth embodiment is different from the above-described embodiments (particularly, the fourth embodiment) in that the refractive index (refractive index spatial distribution) of the light emitting portion 5b ″ is the same as the refractive index of the cladding 2b. And the refractive index of the tip portion 3b ′ on the lens side of the light emitting portion 5b ″ is set higher than the refractive index of the cladding 2b, and the surface of the tip portion 3b ′ (that is, the lens) The point is that the refractive index is gradually set higher as it approaches part 3).

A method of manufacturing such a light radiating portion 5b "will be described. Until the step of forming the refractive index spatial distribution of the light radiating portion 5b" identical and uniform with the refractive index of the cladding 2b shown in FIG. Since it is the same manufacturing method as the third embodiment, it is omitted. Once the light emitting part 5b '' having the same refractive index spatial distribution as the clad 2b and having a uniform refractive index spatial distribution is formed, then the tip part 3b 'is doped with Er, Nd, Ho, Tm, Pr, Sm, Dope Dy, Yb, Ti, etc. and adjust its concentration, so that only the refractive index of the tip 3b ′ is higher than the refractive index of the cladding 2b and gradually approaches the surface of the tip 3b ′. As the doping method, the end of the optical fiber is annealed after ion implantation, the doping material vapor, or the vapor is exposed to a plasma atmosphere, There is a method of immersing the tip 3b ′ in a low-temperature molten glass pool in which a dope material is melted.

Next, the propagation and emission of light in the light irradiation probe 10 will be described with reference to FIG. As shown in FIG. 16, the light propagating from the optical fiber 2 to the light radiating portion 5b ″ has its wavefront gradually changed from a flat surface to a curved surface due to a change in the refractive index spatial distribution, and its mode is radiated from the propagation mode. Furthermore, the wavefront is further converted into a curved surface by the refractive index of the tip portion 3b′.In the fifth embodiment, the refractive index gradually increases as the surface of the tip portion 3b ′ is approached. Since it is formed so as to be higher, the curved surface in the wavefront of the irradiation light emitted from the lens unit 3 to the outside is further tightened compared to the fourth embodiment, and the irradiation range of the external irradiation light is increased. It is further enlarged.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Sixth Embodiment>
Next, a sixth embodiment of the present invention will be described with reference to FIGS. FIG. 17 schematically shows a sixth embodiment of the light irradiation probe 11 according to the present invention. 18 is a cross-sectional view taken along the plane FF of FIG. 17, and FIG. 19 shows light propagation and radiation paths in the light irradiation probe 11 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The sixth embodiment is different from the above embodiments in that the end of the optical fiber 2 has a refractive index (refractive index spatial distribution) different from the refractive index of the core 2a and / or the cladding 2b. The light irradiating probe 11 includes a light-transmitting optical member 12 as the light emitting portion 5c. The refractive index of the optical member 12 is set uniformly. The outer shape of the optical member 12 is formed in a circumferential shape having the same outer diameter as the outer diameter of the clad 2b of the optical fiber 2, and the lens portion 3 is formed at the end thereof. The outer peripheral surface of the optical member 12 is inserted into the cannula 4 like the optical fiber 2 and hermetically sealed with a hermetic seal 6.

  Next, the propagation and emission of light in the light irradiation probe 11 will be described with reference to FIG. As shown in FIG. 19, the light propagated from the optical fiber 2 to the light radiating portion 5c has a propagation mode at the time of incidence on the optical member 12 due to a change in the refractive index of the optical fiber 2 and the light radiating portion 5c. Instead, the wavefront is converted from a flat surface to a curved surface, and diverges inside the optical member 12. The propagating light enters the lens unit 3 and is emitted from the lens unit 3 to the outside of the probe 11 as external radiation light.

  Since the propagation light is converted into the radiation mode inside the optical member 12, the light condensing action in the lens unit 3 is reduced, and the light propagation in the free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Further, the optical member 12 is preferably made of a material whose hardness (for example, Mohs' hardness) is higher than the hardness of the optical fiber 2 and hardly causes wear. This is because by providing a material harder than the optical fiber 2 at the tip of the optical fiber 2 in this way, a material having a hardness suitable for surgery, which is the main application of the light irradiation probe 11, can be used.

  Further, before the propagation light reaches the lens unit 3 which is a light emission unit, the propagation light is emitted inside the optical member 12 to widen the irradiation range of the external irradiation light, so that backscattering of light is suppressed. It becomes possible.

<Seventh embodiment>
Next, a seventh embodiment of the present invention will be described with reference to FIGS. FIG. 20 schematically shows a seventh embodiment of the light irradiation probe 13 according to the present invention. 21 is a cross-sectional view taken along the GG plane of FIG. 20, and FIG. 22 shows light propagation and radiation paths in the light irradiation probe 13 of this embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The seventh embodiment differs from the above-described embodiments, particularly the sixth embodiment, in that the light irradiation probe 13 has the optical member 12 as the light emitting portion 5c ′ at the end of the optical fiber 2. In other words, the refractive index spatial distribution of the optical member 12 is different from the refractive index of the distal end side 12a and the refractive index of the optical fiber end side 12b. As in the sixth embodiment, the optical member 12 is provided at the end of the optical fiber 2, and further, MgO, Er, and Dop as doping materials are provided on the tip end side 12a of the optical member 12 (that is, the lens portion 3 side). By doping Nd, Ho, Tm, Pr, Sm, Dy, Yb, Ti, etc., the refractive index of the tip side 12a is set higher than the refractive index of the end side 12b of the optical fiber. Or, the refractive index of the end side 12b of the optical fiber is set to be higher than the refractive index of the end side 12a by discharging the respective dope materials by heating the tip end side 12a portion after doping. Thus, the refractive index inside the optical member 12 is changed. As the doping method, after the ion implantation, the end of the optical fiber is annealed, or the vapor of the doping material, or the vapor is exposed to a plasma atmosphere, or the molten low temperature molten glass pool in which the doping material is melted is used. There is a method of immersing the tip portion of the optical fiber 2.

  Next, light propagation and radiation in the light irradiation probe 13 will be described with reference to FIG. As shown in FIG. 22, the light propagating from the optical fiber 2 to the light radiating portion 5c ′ has a propagation mode when entering the optical member 12 due to a change in the refractive index of the optical fiber 2 and the light radiating portion 5c ′. The wavefront is changed from a flat surface to a curved surface instead of a radiation mode, and is diverges inside the optical member 12.

  Further, as the wavefront propagates to the lens unit 3 due to a change in the refractive index inside the optical member 12, the propagating light enters the lens unit 3 in a state of being further converted into a curved surface, and the probe is transmitted from the lens unit 3 as external radiation light. 13 is emitted to the outside. Therefore, since the divergence of the propagation light inside the light emitting portion 5c ′ is further expanded compared to the sixth embodiment, the irradiation range of the external irradiation light is further expanded as compared with the sixth embodiment. It becomes possible to do.

  As in the sixth embodiment, the optical member is preferably made of a material whose hardness (eg, Mohs's hardness) is higher than that of the optical fiber 2 and is less likely to be worn.

  Further, before the propagation light reaches the lens unit 3 which is a light emission unit, the propagation light is emitted inside the optical member 12 to widen the irradiation range of the external irradiation light, so that backscattering of light is suppressed. It becomes possible.

<Eighth Embodiment>
Next, an eighth embodiment of the present invention will be described with reference to FIGS. FIG. 23 schematically shows an eighth embodiment of the light irradiation probe 14 according to the present invention. 24 is a cross-sectional view taken along the line HH in FIG. 23, and FIG. 24 shows light propagation and radiation paths in the light irradiation probe 14 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The eighth embodiment is different from the above embodiments in that the present embodiment is a light emitting section having a refractive index spatial distribution in which a part 2b ′ of the cladding 2b is set higher than the refractive index of the core 2a. 5d is formed, and the light emitting probe 14 is provided with the light emitting portion 5d on the end side of the optical fiber 2. As a method for raising the refractive index of the clad 2b ′ part, dope the clad 2b ′ part with molten benzoic acid or MgO, and increase the refractive index by proton exchange, or Er, Nd, Ho, Tm, Pr, Sm, A means for increasing the refractive index by doping Dy, Yb, Ti or the like can be mentioned. As the doping method, the end of the optical fiber is annealed after ion implantation, the end is exposed to the vapor of the doping material, or a plasma atmosphere in which the vapor is converted into plasma, or the doping material is melted at a low temperature. There is a method of immersing the tip portion of the optical fiber 2 in a molten glass pool.

  After the formation of the clad 2b 'part, the end of the optical fiber is cut into a plane by a predetermined dimension, and the cut surface position from the clad 2b' part so that the spread angle of the radiated light from the cut end falls within a certain range. The lens portion 3 is formed by rounding and grinding the tip of the light emitting portion 5d. As described above, the portion from the clad 2b 'portion where the refractive index is changed to the lens portion 3 is formed as the light emitting portion 5d, and the optical fiber 2 is integrally formed from the other clad 2b and the core 2a. Since the cut surface position is ground and polished in a radial manner so that the spread angle of the radiated light falls within a certain range, it is possible to eliminate variations in the external irradiation light.

Next, the propagation and emission of light in the light irradiation probe 14 will be described with reference to FIG.
As shown in FIG. 25, the light propagated from the optical fiber 2 to the clad 2b ′ is totally reflected by the change in the refractive index of the clad 2b ′, and the mode is converted from the propagation mode to the radiation mode. Is converted from a flat surface to a curved surface and diffuses inside the light emitting portion 5d. As the light propagates to the lens unit 3, the refractive index of the clad again returns to the original refractive index (the refractive index of the clad 2b), but since the light has already diffused when propagating to the clad 2b ′, The propagation mode conversion function in the cladding 2b portion of the radiating portion 5d hardly acts on light. The propagating light incident on the lens unit 3 is emitted to the outside of the probe 14 as external radiation light. However, since the light mode is converted into the radiation mode inside the light radiation unit 5d, the light collected by the lens unit 3 is collected. The light effect is reduced and the propagation of light in free space is still kept in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Ninth embodiment>
Next, a ninth embodiment of the present invention will be described with reference to FIGS. FIG. 26 schematically shows a ninth embodiment of the light irradiation probe 15 according to the present invention. FIG. 27 is a cross-sectional view taken along the plane II of FIG. 26, and FIG. 28 shows light propagation and radiation paths in the light irradiation probe 15 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

The ninth embodiment is different from the above embodiments in that the core 2a and an optical fiber configured by surrounding a periphery of the core 2a with a clad 2b having a refractive index lower than that of the core 2a. No. 2 is cut, and the transmission diffusion plate 16 is inserted and arranged. Along with the arrangement of the transmissive diffusion plate 16, the light radiating portion 5f includes the transmissive diffusion plate 16 and a tip portion 5e cut from the optical fiber 2 and formed with the lens portion 3. The tip portion 5e has the same refractive index spatial distribution as the optical fiber 2, and the lens portion 3 is formed at the tip portion. The light irradiation probe 15 has such a refractive index spatial distribution that is distinguished from the optical fiber 2 and the light emitting portion 5f.

  As the material of the transmissive diffusion plate 16, a milky white glass plate is suitable. The outer shape of the transmissive diffusion plate 16 is formed to be the same as the outer shape of the optical fiber 2, and the outer diameter thereof is set to be the same as the outer diameter of the cladding 2b. By inserting the transmission diffusion plate 16 between the optical fiber 2 and the tip portion 5e, the light irradiation probe 15 has a configuration in which a diffusion region is provided between the optical waveguides.

  Next, the propagation and emission of light in the light irradiation probe 15 will be described with reference to FIG. As shown in FIG. 28, the light propagating from the optical fiber 2 to the light radiating portion 5f is diffused by its action when entering the transmission diffusion plate 16, the mode is converted from the propagation mode to the radiation mode, and the wavefront is changed. The plane is gradually converted into a curved surface. Further, the propagating light incident on the lens unit 3 is emitted from the lens unit 3 to the outside of the probe 15 as external radiation light. Since the mode of propagating light is converted into the radiation mode inside the light emitting unit 5f, the condensing action in the lens unit 3 is reduced, and the light propagation in the free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Further, before the propagation light reaches the lens unit 3 which is a light emitting part, the propagation light is diffused by the transmission diffusion plate 16 and its spread angle is increased, and the irradiation range of the external irradiation light is widened. Can be suppressed.

<Tenth Embodiment>
Next, a tenth embodiment of the present invention will be described with reference to FIGS. FIG. 29 schematically shows a tenth embodiment of a light irradiation probe 15 ′ according to the present invention. FIG. 30 is a cross-sectional view taken along the NN plane of FIG. 29, and FIG. 31 shows light propagation and radiation paths in the light irradiation probe 15 ′ of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

The tenth embodiment differs from the above embodiments, particularly the ninth embodiment, in that the core 2a and the clad 2b having a refractive index lower than that of the core 2a are surrounded by the core 2a. The light irradiation probe 15 ′ includes a diffusion portion 65 in which a large number of holes 65a are formed across the cladding 2b and the core 2a, instead of the transmission diffusion plate 16, between the optical fibers 2 formed by surrounding the optical fiber 2. Is a point. As the diffusing portion 65 is included, the light radiating portion 5f ′ includes the diffusing portion 65 and the tip portion 5e ′. The tip portion 5e ′ has the same refractive index spatial distribution as the optical fiber 2, and the lens portion 3 is formed at the tip portion. The light irradiation probe 15 ′ has such a refractive index spatial distribution that is distinguished from the optical fiber 2 and the light emitting portion 5f ′.

  The holes 65a are also formed along the axial direction of the optical fiber 2, and each of the holes 65a is formed in a circular cross section having substantially the same diameter. Since the air holes 65a are filled with air or kept in a vacuum state, the refractive index inside the air holes 65a is set lower than the refractive index of the cladding 2b.

  Such a hole 65a emits ultrashort pulsed light such as a femtosecond laser and condenses it inside the optical fiber 2, and the optical fiber material in the condensing region inside the optical fiber 2 evaporates, resulting in a hole position. Is formed.

  Next, light propagation and radiation in the light irradiation probe 15 'will be described with reference to FIG. As shown in FIG. 31, when the light propagated from the optical fiber 2 to the light emitting portion 5f 'enters the diffusing portion 65, it is diffused due to the presence of the holes 65a. Since the refractive index of the hole 65a is lower than that of the cladding 2b, the light is emitted from the hole 65a at a wide radiation angle, the mode of the propagating light is converted from the propagation mode to the radiation mode, and the wavefront is gradually curved from the plane. It is converted into a shape. Further, the propagating light incident on the lens unit 3 is emitted from the lens unit 3 to the outside of the probe 15 'as external radiation light. Since the mode of the propagating light is converted into the radiation mode in the light emitting section 5f ', the condensing action in the lens section 3 is reduced, and the light propagation in the free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe.

  Further, before the propagation light reaches the lens unit 3 which is a light emitting unit, the propagation light is diffused by the diffusion unit 65 and the spread angle becomes large, and the irradiation range of the external irradiation light is widened. It becomes possible to deter.

<Eleventh embodiment>
Next, an eleventh embodiment of the present invention will be described with reference to FIGS. FIG. 32 schematically shows an eleventh embodiment of the light irradiation probe 17 according to the present invention. 33 is a cross-sectional view taken along the line JJ of FIG. 32, and FIG. 34 shows light propagation and radiation paths in the light irradiation probe 17 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

The eleventh embodiment differs from the above-described embodiments, particularly the third embodiment, in that the refractive index spatial distribution of the light emitting portion 5g is the same as that of the clad 2b and is formed uniformly. In the above, the hollow portion 5g ′ is provided inside the light emitting portion 5g. The inside of the hollow portion 5g ′ is filled with air or kept in a vacuum state. Accordingly, the refractive index inside the hollow portion 5g ′ is set lower than the refractive index of the cladding 2b.

A method for manufacturing such a light emitting portion 5g will be described. First, the central portion (core 2a) of the end portion of the optical fiber is focused by irradiating the femtosecond laser, and the optical fiber material in the condensing region is evaporated to form a hollow portion. The ends are melted by heating and formed into water droplets by surface tension (see FIG. 35). As a result, the end portion of the optical fiber excluding the hollow portion 5g ′ has the same refractive index space distribution as that of the clad 2b. Next, the lens portion 3 is formed by grinding / polishing the end portion of the optical fiber in the form of water droplets up to the one-dot chain line in the figure, and the light emitting portion 5g is formed.

  Next, the propagation and emission of light in the light irradiation probe 17 will be described with reference to FIG. As shown in FIG. 34, the light propagating from the optical fiber 2 to the light radiating portion 5g is converted from the propagation mode to the radiation mode at the end of the core 2a region, and the wavefront gradually changes from the plane. Converted to a curved surface. Further, since the refractive index of the hollow portion 5g ′ formed inside the light emitting portion 5g is lower than that of the cladding 2b, the light further spreads and is diffused at the hollow portion 5g ′, and is emitted from the lens portion 3 to the outside of the probe 17. Is emitted. Accordingly, it is possible to further expand the irradiation range of the external irradiation light as compared with the light irradiation probe 8 of the third embodiment.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Twelfth embodiment>
Next, a twelfth embodiment of the present invention will be described with reference to FIGS. FIG. 36 schematically shows a twelfth embodiment of the light irradiation probe 18 according to the present invention. FIG. 37 is a cross-sectional view taken along the KK plane of FIG. 36, and FIG. 38 shows light propagation and radiation paths in the light irradiation probe 18 of the present embodiment. Further, FIG. 39 shows a cross-sectional view taken along the line LL of FIG. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The twelfth embodiment is different from the above-described embodiments, particularly the eleventh embodiment, as shown in FIG. 39, as a light propagation portion, a central portion 2c that acts as a core and a periphery that acts as a cladding. An optical fiber 2 ′ having a refractive index spatial distribution composed of a portion 2d is used. The optical fiber 2 'is made of quartz or the like, and the central portion 2c has a structure in which the quartz or the like is solid.

  One peripheral portion 2d is formed so that a plurality of hollow pores 2d ′ extending in the axial direction of the optical fiber 2 ′ surround the center portion 2c, and the refractive index thereof is that of the center portion 2c. Since the refractive index is set lower than the refractive index, the light is confined in the central portion 2c and propagated inside the optical fiber 2 ′.

Next, a method for manufacturing the light emitting portion 5g will be described. First, a femtosecond laser is irradiated to the central portion 2c at the end of the optical fiber. At the time of irradiation, the condensing point of the femtosecond laser is aligned with the central portion 2c, and the condensing point is removed from the pore 2d ′, so that the portion of the pore 2d ′ is melted and blocked without being in a hollow state. When the pore 2d 'at the end of the optical fiber is closed in this manner, the center of the end of the optical fiber is then irradiated again with a femtosecond laser to collect light, and the optical fiber material in the condensing region evaporates. A hollow portion is formed to form a hollow portion 5g ′. Thereafter, the end portion of the optical fiber 2 ′ is melted by heating and formed into water droplets by surface tension (see FIG. 40). As a result, the light emitting portion 5g excluding the hollow portion 5g ′ has the same refractive index space distribution as the optical fiber 2 ′, that is, the central portion 2c. Next, the lens portion 3 is formed by grinding / polishing the end portion of the optical fiber in the form of water droplets up to the one-dot chain line in the figure, and the light emitting portion 5g is formed.

  Next, the propagation and emission of light in the light irradiation probe 18 will be described with reference to FIG. As shown in FIG. 38, light enters from the other end (not shown) of the optical fiber 2 ', is confined in the central portion 2c, and propagates in the optical fiber 2' toward the lens portion 3 side. The propagating light propagating through the optical fiber 2 'is held in the propagation mode, and its wavefront is held perpendicularly and parallel to the axial direction of the optical fiber 2'.

The light propagating from the optical fiber 2 ′ to the light radiating portion 5g is converted from a propagation mode to a radiation mode by a change in the refractive index spatial distribution, and the wavefront is gradually converted from a plane to a curved surface. Further, light is emitted at a wider radiation angle at the hollow portion 5g ′ and is emitted from the lens unit 3 to the outside of the probe 18.

  Furthermore, the propagation angle of the propagation light is increased before the propagation light reaches the lens unit 3 and the irradiation range of the external irradiation light is widened, so that it is possible to suppress the backscattering of the light.

<Thirteenth embodiment>
Next, a thirteenth embodiment of the present invention will be described with reference to FIG. FIG. 41 is a left partial side sectional view schematically showing a thirteenth embodiment of the light irradiation probes 25, 26, and 27 according to the present invention. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The thirteenth embodiment may have several forms, as shown in FIG. 41 (a), in which a transmission diffusion plate 16 is provided in the optical fiber 2 as the light propagation section, as shown in FIG. A configuration in which a transmission diffusion plate 16 is provided between the optical fiber 2 and the light emitting portion 5d, or a configuration in which the transmission diffusion plate 16 is provided between the optical fiber 2 and the optical member 12 as shown in FIG. Respectively.

  Propagation and emission of light from the light irradiation probes 25 to 27 are basically the same as those in the ninth embodiment. The light propagated from the optical fiber 2 to the light radiating portions 5b, 5c, 5d is diffused by the transmission diffusion plate 16 and emitted as external radiated light from the lens portion 3 to the outside of the probes 25, 26, 27. Further, in the light irradiation probes 25 to 27, in addition to the transmissive diffusion plate 16, light radiating portions 5b, 5c, and 5d are also provided, so that the propagating light diffused by the transmissive diffusing plate 16 is transmitted to the light radiating portions 5b, Further emitted by 5c and 5d and emitted from the lens unit 3. Accordingly, it is possible to further expand the irradiation range of the external irradiation light as compared with the light irradiation probe 15 of the ninth embodiment.

  Furthermore, before the propagation light reaches the lens unit 3 which is a light emission part, the propagation light is radiated by the transmission diffusion plate 16 to widen the irradiation range of the external irradiation light, so that backscattering of light is suppressed. Is possible.

  Of course, it is possible to change the configuration of FIG. 41B to a configuration in which the transmission diffusion plate 16 is installed in the optical fiber 2 as shown in FIG.

  FIG. 41 shows a mode in which the light diffusing plate 16 is provided in the light irradiation probe of each of the third, sixth, and eighth embodiments. Of course, the other embodiments (the ninth embodiment) The light irradiating probe (except the embodiment) may be cut into the optical fiber, or between the optical fiber and the light emitting portion, and the transmission diffusion plate 16 may be inserted and arranged to form a new light irradiating probe.

<Fourteenth embodiment>
Next, a fourteenth embodiment of the present invention will be described with reference to FIGS. FIG. 42 schematically shows a fourteenth embodiment of the light irradiation probe 19 according to the present invention, where (a) is a plan view, (b) is a left side sectional view, (c) is a bottom view, and (d) ) Shows front views. Further, FIG. 43 is a cross-sectional view cut along the MM plane of FIG. 42, and FIG. 44 shows light propagation and radiation paths in the light irradiation probe 19 of the present embodiment. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The fourteenth embodiment differs from the above-described embodiments, particularly the first embodiment, in that a single flat surface 20 is formed at the tip of the light emitting portion 5a in place of the lens portion 3, and the tip The point is that the part is formed into a sharp shape. The plane 20 is formed non-parallel to the axial direction of the optical fiber 2 that is a light propagation portion, and at an angle of less than 90 degrees. Accordingly, light emission from the optical fiber 2 is as shown in FIG.

  As shown in FIG. 44, the light incident from the other end (not shown) of the optical fiber 2 propagates in the optical fiber 2 toward the light emitting portion 5a. The propagating light propagating through the optical fiber 2 is held in the propagation mode, and its wavefront is held perpendicularly and parallel to the axis of the core 2a.

Next, when light propagates from the optical fiber 2 to the light radiating portion 5a, the refractive index of the core 2a gradually spreads due to the change in the refractive index spatial distribution, and the light radiating portion 5a has almost the same refractive index. Thus, the wavefront is gradually converted from a flat surface to a curved surface. The mode of the propagating light is converted from the propagating mode to the radiation mode. Further, the light propagated to the tip of the light emitting portion 5a is emitted to the outside of the probe 19 as external emitted light. At the time of the emission, the external irradiation light is refracted on the surface of the plane 20 formed obliquely, and is irradiated downward and obliquely to the right as the refraction direction as shown in FIG.

  The mode of the propagating light is converted into a radiation mode inside the light emitting section 5a, and the propagation of light in free space is still held in the radiation mode. Accordingly, it is possible to expand the irradiation range of the external irradiation light as compared with the conventional light irradiation probe. Further, the propagation angle of the propagation light is increased before the propagation light reaches the front end of the light emitting portion, and the irradiation range of the external illumination light is widened, so that it is possible to suppress the backscattering of the light.

  Furthermore, since the tip portion is formed into a sharp shape, when the light irradiation probe 19 is inserted into the eyeball for observation / operation of the fundus, a simple laceration is given to the eyeball surface. Therefore, it is possible to accelerate healing of the eyeball after the light irradiation probe 19 is removed without causing a complicated laceration on the eyeball surface.

  The flat surface 20 is formed by a known general grinding / polishing process. Note that the flat surface 20 may be formed in the same manner as in FIG. 42 on the tip of the light emitting portion of the light irradiation probe or the tip of the optical member described in the above embodiments. As an example, a left side sectional view of a light irradiation probe in which a flat surface 20 is provided in place of the lens portion 3 at the tip of the light emitting portion or the tip of the optical member of each of the second, sixth, and eighth embodiments. The figure is shown in FIG.

  Moreover, although the light irradiation probe 19 provided with one plane 20 is shown as the light irradiation probe 19, a plurality of planes 20 may be changed to be applied to the end of the light emitting portion or the end of the optical member. Further, as another form having a sharp shape, the tip of the light emitting portion may be formed into a conical shape.

<Fifteenth embodiment>
Next, a fifteenth embodiment of the present invention is described with reference to FIG. In addition, the same number is attached | subjected to the same location as each said embodiment, and the overlapping description is abbreviate | omitted or simplified and demonstrated.

  The light irradiation probes 21 and 22 shown in FIG. 46 are different from the above embodiments in that a plurality of steps 23 and 24 are provided at the tip of the light emitting portion 5a. The level difference referred to in the present embodiment refers to a stepped shape, and is not a term indicating a difference in height between the levels. 46 (a) shows a light irradiation probe 21 provided with a plurality of concentric annular steps 23, and FIG. 46 (b) shows a plurality of steps 24 in which the outer shape is combined with an arc and a plane. This is a light irradiation probe 22. FIG. 46 (c) is a side sectional view of FIG. 46 (b).

  Further, by providing the light emitting surface with the steps 23 and 24 formed at the tip of the light emitting portion 5a, the irradiation range of the external irradiation light can be expanded and the lens portion 3 as in the above embodiments. The propagation angle of the propagation light is increased before the propagation light reaches the end, and the irradiation range of the external illumination light is widened, so that backscattering of the light can be suppressed. The steps 23 and 24 may be formed in the same manner as in FIG. 46 on the tip of the light emitting portion of the light irradiation probe described in each of the above embodiments.

  In place of the steps 23 and 24, the tip surface of the light emitting portion of the light irradiation probe of each of the above embodiments is formed in a polished glass shape having a rough surface having a number of fine irregularities, and propagating light is transmitted. You may change so that it may carry out diffuse irradiation.

<Sixteenth Embodiment>
Next, a sixteenth embodiment of the present invention will be described with reference to FIG. FIG. 47 is an explanatory diagram showing a configuration of a fundus oculi observation device or a fundus surgery device 28 (hereinafter, device 28) using the light irradiation probe according to any of the first to fourteenth embodiments. As the probes 29 and 30 in the figure, the light irradiation probe described in any of the first to fifteenth embodiments can be used. This device 28 is used in particular for the treatment of age-related macular degeneration.

  Since the apparatus 28 combines the fundus surgery apparatus and the fundus observation apparatus, the fundus observation can be performed during the fundus surgery. Specifically, the apparatus 28 includes an intraocular illumination probe 29, a photocoagulation probe 30, a light source unit (light source unit) 31, an intraocular observation device 32, and an intraocular monitor unit (intraocular image visualization unit) 33. I have.

  The intraocular illumination probe 29 is connected to the light source unit 31 by an illumination light guide cable. As described in the above embodiments, the optical fiber 2 or 2 ′ is covered with the cannula 4, and a handpiece 34 is provided as shown in FIG. 48 so as to cover a part of the cannula 4. In addition, an annular portion 35 is provided on the distal end portion of the cannula 4, that is, on the outer peripheral surface of the cannula 4 protruding from the handpiece 34, so as to protrude in a ring shape and outward from the outer peripheral surface of the cannula 4. .

  Illumination light input from the light source unit 31 is guided to the probe 29 by the illumination light guide cable and is emitted from the distal end portion of the probe 29. As described above, the light irradiation probe 29 has an irradiation range of external irradiation light by radiation before propagating to the lens unit, radiation inside the optical member, radiation at the tip of the light radiation unit, or diffusion of the transmission diffusion plate. Since it is spread, it is possible to irradiate light on a wide area inside the eye to be examined. Therefore, it becomes easy to find cells / tumors / affected areas that have been marked with a fluorescent agent, and it is possible to efficiently and reliably perform fundus observation by fluorescence fundus imaging.

  The photocoagulation probe 30 is connected to the light source unit 31 by a coagulation light guide cable and has a fiber shape like the intraocular illumination probe 29. Light for photocoagulation input from the light source unit 31 is guided to the photocoagulation probe 30 and emitted from the other end.

  The light source unit 31 includes a light source control unit (light source control unit) 36, a filter operation synchronization unit 37, a light output safety control unit (light output safety control unit) 38, an argon laser light source 39, a laser diode 40 for guide light, a first A laser diode 41, an optical system 42, an illumination light output switch, a coagulation light output switch, an illumination / coagulation switch, and a laser output detector 43 are provided.

  The light source control unit 36 controls the light emission of each light source so that the fundus can be observed during surgery. The filter operation synchronization unit 37 operates the filter switching unit of the intraocular observation device 32 to perform switching to insert or remove the laser light filtration filter 44 in the optical path. This switching control is performed based on the type of light emitted from the light source unit 31.

  The light output safety control unit 38 controls the output of various laser beams used for intraocular illumination so as not to exceed a safety level.

  The argon laser light source 39 is a surgical light source that emits coagulation laser light that is irradiated from the tip of the photocoagulation probe 30 to a target site (operation target site) of the fundus within the eye to be examined, and includes krypton red, argon, A direct krypton yellow laser or the like can be used.

  The first laser diode 41 is an illumination light source (visible laser light source), and emits visible laser light in a wavelength range of green to blue to excite and fluoresce fluorescein, that is, illumination laser light for illuminating the inside of the eye. As the excitation light of fluorescein, laser light in the wavelength range of 465 nm to 490 nm can be suitably used. Therefore, the wavelength of visible laser light in this embodiment is set to about 480 nm.

  The illumination light output switch and the coagulation light output switch are both activation switches for inputting illumination laser light or coagulation laser light from the light source unit 31. The illumination / coagulation switch switches the type of laser light emitted from the light source unit 31, and is also a mode switching means for switching various operation modes of the fundus surgery device 28.

  The intraocular observation device 32 includes an objective lens 45, a variable power lens 46, a filter unit 47, an observation light separation unit 48, an eyepiece lens 49, an imaging mirror 50, and a side endoscope 51. The observation light separating unit 48 is provided with at least a beam splitter, and the observation light from the eye to be inspected received through the objective lens 45, the variable power lens 46, and the filter unit 47 is on the eyepiece lens 49 side and the imaging mirror 50 side. It is separated to the side endoscope 51 side.

  The optical system of the intraocular observation device 32 is provided so as to form two optical paths so as to correspond to both eyes of the operator, and almost all of the optical parts such as various lenses except for the objective lens 45 are two. One is provided in the optical path.

  The intraocular monitor unit 33 includes a CCD camera (imaging unit) 52, a recording unit (image recording unit) 53, a display unit (display unit) 54, and a monitor control unit.

  Hereinafter, a surgical procedure by the apparatus 28 is shown. First, in-situ observation by fluorescence detection is performed. After injecting a fluorescent agent, fluorescein, from the elbow vein of the subject, the intraocular illumination probe 29 is inserted into the eyeball, and the fundus is observed with a surgical microscope. The position of the tip of the intraocular illumination probe 29 to be inserted is almost directly below the eyeball insertion hole, but the intraocular illumination probe 29 is provided with the annular portion 35 as described above. It is possible to avoid a situation in which the surgeon unintentionally excessively pushes the intraocular illumination probe 29 into the eyeball. The annular portion 35 may be integrated with the cannula 4 or may be separate from the cannula 4. The material is not particularly limited as long as the material has a strength capable of functioning as an excessive push-in stopper for the intraocular illumination probe 29 and does not adversely affect the eye to be examined.

  480 nm light is incident on the intraocular illumination probe 29. Since the fluorescence of fluorescein has a peak at a wavelength of 515 nm, retinal vascular tissue appears as fluorescence and at the same time pulsation is seen. Therefore, the cause of the lesion in the affected area is determined according to a known fundus contrast diagnosis method. Examples of fundus contrast diagnosis include diagnosis by fluorescein fluorescence contrast, diagnosis by indocyanine green fluorescence contrast, or diagnosis by optical coherence tomography.

  After investigating the cause of the lesion, the operator operates the illumination / coagulation switch to select the single operation mode. As a result, a solidified laser beam can be output from the argon laser light source 39. The operator pulls out the intraocular illumination probe 29 from the eye and inserts the photocoagulation probe 30 into the eye. After the insertion, the surgeon uses cells such as krypton red, argon, direct, krypton, and yellow laser as coagulation laser light from the argon laser light source 39 through the photocoagulation probe 30 to mark cells / tumors / affected areas. Irradiate and perform surgery. As the surgical method, a known extrafoveal photocoagulation method, foveal photocoagulation method, photodynamic therapy, transpupillary thermotherapy, and the like are suitable.

  As the fluorescent agent, in addition to fluorescein, a fluorescent agent that applies fluorescence resonance energy transfer, oregon green, or indocyanine green may be used.

The light irradiation probe of the present invention broadens the irradiation range of external irradiation light by radiation before propagating to the lens part, radiation inside the optical member, radiation at the tip of the light radiation part, or diffusion of the transmission diffusion plate. Therefore, backscattering of light can be suppressed. Therefore, in the apparatus 28 to which this light irradiation probe is applied, it is possible to prevent the occurrence of flare due to the fine particles in the body fluid or Ringer's solution located behind the end of the optical fiber. This makes it possible to provide an apparatus that can obtain an image with a so-called “missing”.

<Seventeenth embodiment>
Next, a seventeenth embodiment of the present invention will be described with reference to FIG. FIG. 49 is a partial cross-sectional view schematically showing the configuration of the endoscope 55 using the light irradiation probe according to any one of the first to fifteenth embodiments. The light irradiation probe described in any of the first to fourteenth embodiments is used for the probe 56 in the drawing.

  As shown in FIG. 49, the optical system of the endoscope 55 is housed in an optical seal case 57. At the distal end portion of the endoscope 55, the optical system, the probe 56, the fiber guide 66, the distal end of the optical fiber 59 constituting the probe 56, and the annular portion 35 (see FIG. 48) are provided inside the metal case 58. ing. The rear part is made of an elastic sheath 60, and is provided with an optical fiber storage pipe 61 and a Ringer's solution inlet 62. The optical fiber 59 is taken in and out of the optical fiber storage pipe 61, whereby the tip of the optical fiber 59 approaches the affected part or is stored in the metal case 58. The optical fiber 59 is inserted and removed by pushing and pulling from the outside. As the optical fiber 59 is taken in and out, Ringer's solution is additionally injected or overflowed and discarded. The optical system includes a lens 63 and a camera 64, and the camera 64 that can output an electrical signal by CCD or CMOS is preferable for in-situ observation.

The light irradiation probe of the present invention can suppress the backscattering of light because the irradiation range of the external irradiation light is expanded by the radiation inside the optical fiber or the optical member, or the radiation of the transmission diffusion plate. Become. Therefore, in the apparatus (endoscope 55) to which this light irradiation probe is applied, it is possible to prevent the occurrence of flare due to the body particles located behind the end of the optical fiber 59 or the fine particles in the Ringer's solution. This makes it possible to provide an apparatus that can obtain an image with a so-called “missing”.

  Furthermore, according to the light irradiation probe of the present invention, a wide irradiation range of the external irradiation light can be secured, so that it becomes easy to find a cell / tumor / affected area marked with a fluorescent agent.

  By using the light irradiation probe of the present invention for a device for observing the eyeball of a subject, an ophthalmic surgery, an endoscope, or the like, light can illuminate a specific cell, a diseased cell, a tumor, or an affected area in a wide irradiation range. This makes it possible to easily detect cells, tumors, affected areas, etc. that have been marked with a fluorescent agent.

(a) The top view which represents typically 1st Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the first embodiment. (c) Front view schematically showing the first embodiment. Sectional drawing which cut | disconnected Fig.1 (a) by the AA surface. The schematic diagram showing the propagation of light and the radiation | emission path | route in the light irradiation probe of FIG. (a) The top view which represents typically 2nd Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the second embodiment. (c) The front view which represents the 2nd Embodiment typically. Sectional drawing which cut | disconnected Fig.4 (a) by the BB surface. The schematic diagram showing the propagation of light and the radiation | emission path | route in the light irradiation probe of FIG. (a) The top view which represents typically 3rd Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the third embodiment. (c) Front view schematically showing the third embodiment. Sectional drawing which cut | disconnected Fig.7 (a) by CC plane. FIG. 8 is a schematic diagram illustrating light propagation and radiation paths in the light irradiation probe of FIG. 7. Explanatory drawing which shows the manufacturing method of the refractive index structure of the optical fiber which concerns on the light irradiation probe of FIG. (a) The top view which represents typically 4th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the fourth embodiment. (c) Front view schematically showing the fourth embodiment. Sectional drawing which cut | disconnected Fig.11 (a) by the DD plane. FIG. 12 is a schematic diagram illustrating light propagation and radiation paths in the light irradiation probe of FIG. 11. (a) The top view which represents typically 5th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the fifth embodiment. (c) Front view schematically showing the fifth embodiment. Sectional drawing which cut | disconnected Fig.14 (a) by the EE surface. FIG. 15 is a schematic diagram illustrating light propagation and radiation paths in the light irradiation probe of FIG. 14. (a) The top view which represents typically 6th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the sixth embodiment. (c) Front view schematically showing the sixth embodiment. Sectional drawing which cut | disconnected Fig.17 (a) by the FF surface. FIG. 18 is a schematic diagram illustrating light propagation and radiation paths in the light irradiation probe of FIG. 17. (a) The top view which represents typically 7th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the seventh embodiment. (c) The front view which represents typically the said 7th Embodiment. Sectional drawing which cut | disconnected Fig.20 (a) by the GG plane. The schematic diagram showing the propagation of light and the radiation | emission path | route in the light irradiation probe of FIG. (a) The top view which represents typically 8th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the eighth embodiment. (c) Front view schematically showing the eighth embodiment. Sectional drawing which cut | disconnected Fig.23 (a) by the HH surface. FIG. 24 is a schematic diagram showing light propagation and radiation paths in the light irradiation probe of FIG. 23. (a) The top view which represents typically 9th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the ninth embodiment. (c) Front view schematically showing the ninth embodiment. Sectional drawing which cut | disconnected Fig.26 (a) by the II surface. FIG. 27 is a schematic diagram showing light propagation and radiation paths in the light irradiation probe of FIG. 26. (a) The top view which represents typically 10th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the tenth embodiment. (c) Front view schematically showing the tenth embodiment. Sectional drawing which cut | disconnected Fig.29 (a) by the NN plane. FIG. 30 is a schematic diagram showing light propagation and radiation paths in the light irradiation probe of FIG. 29. (a) The top view which represents typically 11th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the eleventh embodiment. (c) A front view schematically showing the eleventh embodiment. Sectional drawing which cut | disconnected Fig.32 (a) by the JJ plane. FIG. 33 is a schematic diagram showing light propagation and radiation paths in the light irradiation probe of FIG. 32. Explanatory drawing which shows the manufacturing method of the refractive index structure of the light emission part which concerns on the light irradiation probe of FIG. (a) The top view which represents typically 12th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the twelfth embodiment. (c) The front view which represents typically the 12th embodiment. Sectional drawing which cut | disconnected Fig.36 (a) by the KK plane. FIG. 37 is a schematic diagram illustrating light propagation and radiation paths in the light irradiation probe of FIG. 36. Sectional drawing which cut | disconnected Fig.36 (a) by the LL surface. Explanatory drawing which shows the manufacturing method of the refractive index structure of the optical fiber which concerns on the light irradiation probe of FIG. The left view which represents typically 13th Embodiment of the light irradiation probe which concerns on this invention. (a) The top view which represents typically 14th Embodiment of the light irradiation probe which concerns on this invention. (b) Left partial side sectional view schematically showing the fourteenth embodiment. (c) A bottom view schematically showing the fourteenth embodiment. (d) Front view schematically showing the fourteenth embodiment. Sectional drawing which cut | disconnected Fig.42 (a) by the MM surface. The schematic diagram showing the propagation of light and the radiation | emission path | route in the light irradiation probe of FIG. (a) The left part side sectional view of the light irradiation probe which gave the plane to the end of the light emission part of a 2nd embodiment. (b) The left part side sectional view of the light irradiation probe which gave a plane to the end of the optical member of a 6th embodiment. (c) The left part side sectional view of the light irradiation probe which gave the plane to the end of the light emission part of an 8th embodiment. (a) A left side sectional view schematically showing a fifteenth embodiment of the light irradiation probe according to the present invention. (b) Left partial side sectional view schematically showing another form of the fifteenth embodiment. (c) Side sectional view of FIG. Explanatory drawing which shows the structure of a fundus observation or a fundus surgery device using the light irradiation probe according to any one of the above embodiments. The left partial sectional view which represents typically the light irradiation probe of this invention in which the handpiece and the annular part were provided in the cannula. The fragmentary sectional view which shows typically the structure of the endoscope using the light irradiation probe in any one of said each embodiment. (a) The fragmentary sectional side view of the conventional light irradiation probe. (b) Front view corresponding to FIG. Explanatory drawing showing generation | occurrence | production of the backscattered light in the light irradiation probe of FIG.

Explanation of symbols

1, 7, 8, 9, 10, 11, 13, 14, 15, 15 ', 17, 18, 19, 21, 22, 25, 26, 27 Light irradiation probe 2, 2', 59 Optical fiber
2a core
2b, 2b 'clad
2c center
2d peripheral
2d 'Pore 3 Lens part
3a, 3b, 3b 'tip 4 cannula
5a, 5a ', 5b, 5b', 5b ”, 5c, 5c ', 5d, 5f, 5f', 5g
5e Tip
5g 'hollow 6 hermetic seal
12 Optical components
12a Tip side
12b End of optical fiber
16 Transmission diffuser
20 plane
23,24 steps
28 Fundus observation device or fundus surgery device
29 Intraocular probe
30 Photocoagulation probe
31 Light source
32 Intraocular observation device
33 Intraocular monitor
34 Handpiece
35 torus
36 Light source controller
37 Filter operation synchronization section
38 Light output safety control unit (light output safety control means)
39 Argon laser light source
40 Laser diode for guide light
41 First laser diode
42 Optics
43 Laser output detector
44 Laser filter
45 Objective lens
46 Variable magnification lens
47 Filter section
48 Observation beam separator
49 Eyepiece
50 Imaging mirror
51 Sidescope
52 CCD camera (imaging means)
53 Recording unit (image recording means)
54 Display (display means)
55 Endoscope
56 Probe
57 Optical seal case
58 metal case
60 Elastic sheath
61 Optical fiber storage pipe
62 Ringer solution inlet
63 lenses
64 cameras
65 Spreading section
65a hole
66 Fiber guide

Claims (3)

A light propagation part and a light emission part in an optical fiber axial direction , wherein the refractive index spatial distribution of the light emission part is different from the refractive index spatial distribution of the light propagation part, the light propagation part being a core and a refraction of the core; An optical fiber having a configuration in which a clad having a refractive index lower than the refractive index surrounds the periphery of the core;
The light radiating portion has the same refractive index spatial distribution as the refractive index of the core, and Er, Nd, Ho, Tm, Pr, Sm, Dy, Yb, and Ti are lenses of the light radiating portion. The tip is doped with the tip, the tip has a refractive index higher than the refractive index of the core, and the light emitting portion is further provided on the end of the optical fiber ,
The wavefront of light is converted from a flat surface into a curved surface in the optical fiber axis direction, and further converted into a curved surface at the distal end to irradiate light, and used for a fundus oculi observation device, a fundus surgery device or an endoscope. A light irradiation probe characterized by. The light irradiation probe according to claim 1,
One or a plurality of planes are formed at the tip of the light emitting part at an angle less than 90 degrees non-parallel to the axial direction of the light propagating part. . The light irradiation probe according to claim 1,
The light irradiation probe is characterized in that a tip of the light emitting portion is formed in a conical shape.

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