JP3650364B2 - Optical scanning probe device - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention transmits light through a light transmission means in an optical probe, scans light focused and irradiated from the tip to the test portion side, detects return light from the focal position, and detects optical image information. The present invention relates to an optical scanning probe device for obtaining
[0002]
[Prior art]
In recent years, unlike a normal optical microscope that optically magnifies and observes a subject, a confocal microscope that obtains optical information of the focal position by scanning the focal point on the side of the subject under a confocal relationship is provided. For example, it is disclosed in WO 90/00754.
[0003]
This prior art discloses an optical scanning microscope having different focal lengths by arranging two types of objective lenses having different focal lengths in parallel, moving the optical system and selectively using the two types of objective lenses.
[0004]
[Problems to be solved by the invention]
However, the above prior art cannot change the focal position on the optical axis of one objective lens, and there is no means for continuously moving the focal point in the depth direction on the same optical axis.
That is, in the conventional technique, when the focus position is moved in the depth direction with respect to the part to be examined, the observation position is also changed when the objective lens as the condensing means is changed from one to the other. Therefore, it is inconvenient to examine the part to be examined along the depth direction.
In addition, since the focal point cannot be continuously moved in the depth direction, a tomographic image and three-dimensional information cannot be obtained.
[0005]
The present invention has been made in view of the above points, and an object of the present invention is to provide an optical scanning probe apparatus capable of obtaining an observation image along a depth direction of a portion to be examined.
[0006]
Another object of the present invention is to provide an optical scanning probe apparatus capable of continuously moving the focal point in the optical axis direction.
[0007]
[Means for Solving the Problems]
In order to achieve the above object, an optical scanning probe apparatus according to claim 1, wherein an optical probe inserted into a body cavity, a light source for generating light for irradiating light to a test part, and light from the light source A light transmitting means for guiding the light to the tip of the optical probe, a light collecting means for condensing and irradiating the light to the test part, and a focus focused on the test part side by the light collecting means An optical scanning unit that scans in a direction perpendicular to the optical axis direction, a separating unit that separates return light from the test portion from light from a light source, and a light detecting unit that detects the separated light. Provided with a changing means for changing the position of the focal point condensed on the test portion side along the optical axis direction of the condensing means.
[0008]
DETAILED DESCRIPTION OF THE INVENTION
Embodiments of the present invention will be described below with reference to the drawings.
(First embodiment)
1 to 5 relate to a first embodiment of the present invention, FIG. 1 shows the overall configuration of the optical scanning probe apparatus of the first embodiment, and FIG. 2 shows the configuration of the tip of the optical probe. 3 shows the configuration of the optical unit, FIG. 4 shows the configuration of the control unit, and FIG. 5 shows the state of focus scanning when the movable mirror is driven.
[0009]
As shown in FIG. 1, the optical scanning probe device 1 according to the first embodiment of the present invention can be inserted into a body cavity or the like, a light source unit 2 that generates light, a light transmission unit 3 that transmits the light, and the like. And an optical probe 4 for emitting light passing through the light transmission unit 3 from the tip side to the subject side and guiding the return light to the light transmission unit 3, and return light from the optical probe 4 And a control unit 5 that performs signal processing to detect and image the light through the light transmission unit 3 and control of the optical scanning means provided in the optical probe 4.
[0010]
The light source unit 2 is configured by a laser oscillation device that outputs laser light, for example. An argon laser having a wavelength of 488 mm is suitable for cell observation.
The optical transmission unit 3 includes optical transmission fibers (simply abbreviated as “fibers”) 6a, 6b, 6c, and 6d, and a four-terminal coupler 7 that bifurcates them and optically couples them. The fibers 6a, 6b, 6c, and 6d are single mode fibers.
[0011]
The end of the fiber 6a is connected to the light source unit 2, the end of the fiber 6c is connected to the control unit 5, and the end of the fiber 6d is connected to a non-reflective device or the like (closed).
[0012]
The fiber 6b is long and is guided to the tip end portion 9 through, for example, the inside of the flexible tube 8 constituting the outer tube of the optical probe 4. For example, the light tube 4 can be inserted into a body cavity inserted into a treatment instrument channel of an endoscope.
[0013]
As shown in FIG. 2, the distal end portion 9 includes an annular rigid optical frame 10 with one end attached to the distal end of the tube 8, an optical unit 11 attached inside the optical frame 10, and an optical frame. And a tip cover 12 (transparent and hard) as a transparent window member pressed against an object attached to the tip of the pin 10 via a piezoelectric element 28 described later.
[0014]
The tip of the optical fiber 6b inserted into the tube 8 is fixed to the optical unit 11, and the light emitted from the tip of the optical fiber 6b is to be inspected via the optical scanning mechanism (scanner) on the side of the test part 13 The light is condensed and irradiated, and the return light is received.
[0015]
FIG. 3 shows a detailed configuration of the optical unit l1.
The optical unit 11 includes a substrate 14, a spacer 15 provided on the upper surface thereof, and an upper plate 16 provided on the upper surface of the spacer 15. The substrate 14 is provided with two movable mirrors (also called rotating mirrors) 17 and 18 whose directions are variable in order to scan the laser beam toward the object side.
[0016]
The two movable mirrors 17 and 18 are supported by two hinge portions 17a and 18a, and the movable mirrors 17 and 18 are configured to be rotatable by electrostatic force by electrodes (not shown).
[0017]
A ground electrode (not shown) facing these electrodes is connected to the control unit 5 via a cable 19. Further, the rotational axes of the two movable mirrors 17 and 18 are configured to be orthogonal to each other. Further, the spacer 15 has a mirror 21 at a portion facing the end face of the fiber 6b, the upper plate 16 has a mirror 22, and a diffraction grating lens for condensing the laser beam and converging the focal point 23 to the test portion 13 side. 24 is provided.
[0018]
The diffraction grating lens 24 has a function corresponding to a lens having a very short focal length due to a diffraction phenomenon. Therefore, the focal point 23 is two-dimensionally scanned in a direction perpendicular to the depth direction of the test portion 19. Thus, it is possible to obtain a microscopically magnified image of the portion 13 to be examined.
[0019]
The optical fiber 6b of the four-terminal coupler 7 is fixed between the substrate 14 and the spacer 15 as shown in FIG.
Then, a driving signal is applied to the movable mirrors 17 and 18 (electrodes thereof), and the focal points 23 are scanned two-dimensionally on the scanning surface 25 by rotating the hinges 17a and 18a with appropriate rotation angles. I can do it.
[0020]
For example, when the movable mirror 17 is driven, the light is scanned in the X direction 26 in the direction perpendicular to the paper surface of FIG. 2, and when the movable mirror 18 is driven, the light is scanned in the Y direction 27 in the horizontal direction in FIG. Is done. In other words, the movable mirrors 17 and 18 are moved so that the focal point 23 on the test portion 13 side can be two-dimensionally scanned on the scanning surface 25 perpendicular to the depth direction (Z direction). A confocal microscope capable of obtaining reflected light information on the surface 25 is formed.
[0021]
One end of a small plate-like or rod-like piezoelectric element 28 is bonded to the optical frame 10 at, for example, four orthogonal positions in the circumferential direction, and the base end of the tip cover 12 is bonded to the other end of the piezoelectric element 28. The piezoelectric element 28 is connected to the control unit 5 through the cable 19.
[0022]
Then, by applying a drive signal to the piezoelectric element 25, the piezoelectric element 28 is contracted in the Z direction, which is the depth direction of the test portion 13, as indicated by reference numeral 29 in FIG. The cutting surface 30 shown by can be varied in the Z direction.
The tip cover 12 is made of a transparent material cover such as polycarbonate.
[0023]
FIG. 4 shows the configuration of the control unit 5.
The control unit 5 includes a laser drive circuit 31 that drives the light source unit 2, an XY drive circuit 32 that drives the movable mirrors 17 and 18 of the optical probe 4, a Z drive circuit 33, a photo detector 34 that includes an amplifier, and a confocal point. The image processing circuit 35 that performs image processing for generating an image, a monitor 36 that displays the image processed image, and a recording device 37 that records the image as necessary. So connected.
[0024]
The laser drive circuit 31 is connected to the light source unit 2 by a cable 38. In addition, the XY control circuit 32 is connected to the electrodes of the movable mirrors 17 and 18 and the ground electrode facing them via the cables 19.
[0025]
Further, the Z drive circuit 33 is connected to the piezoelectric element 28 via the cable 19 and corresponds to the operation amount to be tilted by performing an operation of changing a focus position changing operation means such as a joystick (not shown). The Z drive circuit 33 applies a drive signal to the piezoelectric element 28 and contracts it by an amount corresponding to an operation amount for tilting the piezoelectric element 28.
[0026]
As shown in FIG. 2, the piezoelectric element 28 contracts in a state where the tip cover 12 is pressed against the test portion 13, so that the position of the focal point 23 when the focused irradiation is performed on the test portion 13 side. It can be changed along the optical axis direction of the condensing means (that is, along the depth direction of the test part 13).
[0027]
In other words, in the present embodiment, the distal end portion 9 of the optical probe 4 is focused and irradiated so that the focal point 23 is formed on the test portion 13 side, and the focal point 23 is orthogonal to the depth direction of the test portion 13. A scanning unit that scans on the scanning surface 25 to obtain confocal microscope image information, and a moving unit that continuously moves the position of the focal point 23 in the depth direction of the test portion 13. A feature is that means for changing the position of the focal point 23 in the optical axis direction of the diffraction grating lens 24 is provided.
[0028]
Next, the operation of this embodiment will be described.
When the present optical probe 4 is used, the distal end surface of the distal end cover 12 at the distal end of the optical probe 4 is pressed against a portion to be inspected. At this time, the test portion 13 is fixed with respect to the distal end portion 9 of the optical probe 4 and image blurring can be reduced.
[0029]
The laser device forming the light source unit 2 driven by the laser driving circuit 31 generates laser light, and this light is incident on the optical fiber 6a. This light is divided into two parts by the four-terminal coupler 7, one of which is guided to the closed end and no return light is present, and the other light is passed through the optical fiber 6b to the tip 9 of the probe 4. Led to.
[0030]
As shown in FIG. 2, this laser light exits from the end face (a small area portion) of the thin fiber 6b, is reflected by the mirror 21 disposed on the opposite side, and is movable on the reflected light side. The light is reflected by the mirror 17, subsequently reflected by the mirror 22 arranged on the reflected light side, and further reflected by the movable mirror 18 arranged on the reflected light side.
[0031]
Subsequently, after passing through the diffraction grating lens 24, passing through the tip cover 12, it is focused and irradiated on the test portion 13 side so as to form the focal point 23. Further, the backscattered light from the focal point 23 passes through the same optical path as the incident light and enters the fiber 6b again. Backscattered light from other than the focal point 23 cannot pass through the same optical path as the incident light, and therefore cannot be focused on the tip surface of the pinhole-shaped fiber 6b. Cannot enter the tip surface.
[0032]
That is, the present optical probe device 1 forms a confocal optical system in which the focal point 23 and the distal end surface of the fiber 6b are in a confocal relationship, and constitutes an optical system that detects only the return light from the focal point 23.
[0033]
Further, when the movable mirror 17 is rotated by the XY drive circuit 32 of the control unit 5 in this state, the position of the focal point 23 of the laser beam is accordingly in the X direction indicated by reference numeral 26 on the scanning surface 25 (perpendicular to the paper surface). Scanned.
[0034]
When the rotating mirror 18 is rotated, the position of the focal point 23 of the laser beam is scanned in the Y direction indicated by reference numeral 27 on the scanning surface 25 accordingly. Here, by making the frequency of vibration in the Y direction sufficiently slower than the frequency of scanning in the X direction, the focal point 23 sequentially raster scans the scanning surface 25 as shown in FIG. Accordingly, the back scattered light at each point on the scanning surface 25 is transmitted by the optical fiber 6b.
[0035]
The light incident on the fiber 6b is divided into two by the four-terminal coupler 7, guided to the photodetector 34 of the controller 5 through the fiber 6c, and detected by the photodetector 34.
[0036]
Here, the photodetector 34 outputs an electrical signal corresponding to the intensity of incident light, and is further amplified by a built-in amplifier (not shown). This signal is sent to the image processing circuit 35. The image processing circuit 35 refers to the drive waveform of the XY drive circuit 32 to calculate the signal output at which the focal position is, and further calculates the intensity of the backscattered light at this point. By repeating, the backscattered light on the scanning surface 25 is imaged and displayed on the monitor 36. Further, the image data is recorded in the recording device 37 as necessary.
[0037]
For a confocal microscope image of this part, for example, when there is a possibility that the part is a lesioned part, if you want to examine the state of the part in more detail, operate the focal position change operation means (not shown), The position of the focal point 23 in the test part 13 is changed in the depth direction.
[0038]
In other words, when it is desired to move the scanning surface 25 in the depth direction with respect to the test portion 13, a drive instruction signal is sent to the Z drive circuit 33 to control the contraction of the piezoelectric element 28. As a result, the piezoelectric element 28 expands and contracts in the Z direction indicated by reference numeral 29, and the tip cover 12 moves in the Z direction accordingly.
[0039]
At this time, the position of the focal point 23 does not move, but the position of the focal point 23 in the test portion 13 is changed to another depth position by moving the position of the tip cover 12 in the Z direction, and the position is observed. Will be able to. At this time, since the position change amount in the depth direction of the tip cover 12 can be measured from the voltage applied to the piezoelectric element 28, it is also understood at which depth the image is obtained.
[0040]
If, for example, only the movable mirror 17 is driven by the XY drive circuit 32, the movable mirror 18 is stopped, and the piezoelectric element 28 is driven slowly by the Z drive circuit 33 instead, the focal point 23 is cut in the depth direction. It is possible to scan the surface 30 two-dimensionally to obtain the two-dimensional image information of the cut surface 30, that is, tomographic image information. The state in which the cut surface 30 is scanned two-dimensionally is shown in FIG. 5, if the Y direction is the Z direction, the scan surface 25 is scanned by the cut surface 30.
[0041]
As described above, the light incident on the fiber 6b is divided into two by the four-terminal coupler 7, detected by the photodetector 34, and the electric signal is input to the image processing circuit 35. In the image processing circuit 35, XY Referring to the drive waveforms of the drive circuit 32 and the Z drive circuit 33, calculate the signal output at which the focal position is, calculate the intensity of backscattered light at this point, and repeat these As a result, the back scattered light of the cut surface 30 is imaged and displayed on the monitor 36. Further, the image data is recorded in the recording device 37 as necessary.
[0042]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
[0043]
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
[0044]
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move relative to the tip of the optical probe 4.
[0045]
Since the position of the focal point 23 of the laser beam is configured to be continuously movable relative to the depth direction of the test part 13, observation images of various depth surfaces of the test part 13 are obtained. This is useful for examining and diagnosing the test object in detail. A tomographic image can also be obtained.
[0046]
(Second Embodiment)
Next, a second embodiment of the present invention will be described with reference to FIG. This embodiment is a modification of the configuration of the first embodiment, and only the focal point moving means in the Z direction is different. Description of other parts is omitted.
In this embodiment, there is no piezoelectric element 28, and the transparent tip cover 12 is bonded to the optical frame 10.
[0047]
A liquid crystal lens 40 is fixed to the inner surface of the tip cover 12. Inside the liquid crystal lens 40, for example, two liquid crystal cells 41 and 42 in the shape of plano-convex lenses filled with liquid crystal are provided. The liquid crystal cells 41 and 42 are fixed to glass plates 43 and 44, respectively, and a glass portion 45 is filled between them.
[0048]
Further, transparent electrodes (not shown) are arranged on the upper and lower surfaces of the liquid crystal cell 41, respectively, and these are insulated from each other. When a voltage is applied between the transparent electrodes, the arrangement of the liquid crystal molecules in the liquid crystal cell 41 changes and the refractive index changes. The same applies to the liquid crystal cell 42. The wiring from these electrodes is connected to the Z drive circuit 33 of the control unit 5 shown in FIG.
Other configurations are the same as those of the first embodiment.
[0049]
Next, the operation of this embodiment will be described.
By changing the voltage applied to the transparent electrodes of the liquid crystal cells 41 and 42 by the Z drive circuit 33, the refractive index of the liquid crystal cells 41 and 42 is changed, and accordingly, the position of the focal point 23 can be moved in the Z direction 29. it can.
[0050]
This makes it possible to observe another depth of the test part 13. Further, here, for example, when only the movable mirror 17 is driven by the XY drive circuit 32 and the movable mirror 18 is stopped, and instead the refractive index of the liquid crystal cells 41 and 42 is slowly driven by the Z drive circuit 33, the focal point 23 becomes deep. The cut surface 30 cut in the direction can be scanned, and the cut surface 30 can be imaged.
[0051]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move with respect to the tip of the optical probe 4.
[0052]
Since the focal point 23 of the laser beam is configured to be relatively movable with respect to the depth direction of the test part 13, the surface of the test part 13 having various depths can be observed. A tomographic image can also be obtained.
Since the liquid crystal lens 40 is used for the movement of the focal point 23 in the optical axis direction, the movement of the focal point 23 in the optical axis direction can be realized with a simpler configuration than in the first embodiment.
[0053]
(Third embodiment)
Next, a third embodiment of the present invention will be described with reference to FIG.
The present embodiment has a configuration obtained by modifying the second embodiment. Specifically, the liquid crystal lens 40 is merely changed to a deformable lens 50 as a variable focus lens that changes its shape, so that other parts are described. Is omitted.
[0054]
That is, the deformable lens 50 is fixed to the inner surface of the distal end cover 12, and the focal point of the deformable lens 50 is changed by changing the shape of the deformable lens 50.
[0055]
Inside the deformable lens 50, a plurality of drive diaphragms 51 and 52 (only two of them are shown in the figure) are provided around the central portion thereof. Plate-like piezoelectric elements 53 and 54 are attached to the diaphragms 51 and 52, respectively. In addition, a lens portion 55 made of a thin film is also provided at the center of the plurality of diaphragms 51 and 52 on the peripheral side of the deformable lens 50.
[0056]
Further, the inside of the deformable lens 50 is filled with a transparent working fluid 56. The wiring from the piezoelectric elements 53 and 54 is connected to the Z drive circuit 33 of the control unit 5 shown in FIG.
[0057]
When a voltage is applied to the piezoelectric elements 53 and 54, the diaphragms 51 and 52 swell, and when the voltage is turned off, the shape becomes almost flat. (In FIG. 7, the voltage is applied.) In addition, the lens portion 55 of the deformable lens 50 is deformed accordingly. At this time, the lens portion 55 has a film thickness so as to have an appropriate convex lens shape. It has a distributed configuration.
[0058]
Next, the operation of this embodiment will be described.
By changing the voltage applied to the piezoelectric elements 53 and 54 by the Z drive circuit 33, the drive diaphragms 51 and 52 expand, and accordingly, the curvature of the deformable lens 50 decreases, and the focal point 23 becomes the deformable lens 50. Move away from Conversely, when the voltage applied to the piezoelectric elements 53 and 54 is lowered, the drive diaphragms 51 and 52 become flat, and accordingly, the curvature of the deformable lens 50 increases and the focal point 23 moves in a direction closer to the deformable lens 50. To do.
[0059]
In this way, the position of the focal point 23 can be moved in the Z direction 29. This makes it possible to observe another depth of the test part 13. Further, here, for example, only the movable mirror 17 is driven by the XY drive circuit 32, the movable mirror 18 is stopped, and when the piezoelectric elements 53 and 54 are slowly driven instead by the Z drive circuit 33, the focal point 23 is moved in the depth direction. The cut surface 30 can be scanned and the cut surface 30 can be imaged.
[0060]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
[0061]
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move with respect to the tip of the optical probe 4.
Since the focal point 23 of the laser beam is configured to be relatively movable with respect to the depth direction of the test part 13, the surface of the test part 13 having various depths can be observed. A tomographic image can also be obtained.
[0062]
Since the deformable lens 50 is used to move the focal point 23 in the optical axis direction, the focal point 23 can be moved in the optical axis direction with a simpler configuration than in the first embodiment.
[0063]
(Fourth embodiment)
Next, a fourth embodiment of the present invention will be described with reference to FIG.
This embodiment is a modification of the first embodiment, and only the means for moving the tip cover 12 is changed, and the description of the other parts is omitted.
[0064]
In the present embodiment, the tip cover 12 and the optical frame 10 are fitted, and the tip cover 12 is movable in the depth direction 29. In addition, an O-ring 60 is provided at a fitting portion between the tip cover 12 and the optical frame 10 to form a watertight structure that keeps watertight inside.
[0065]
The optical frame 10 is provided with a hole 61 in its axial direction, and this hole 61 is connected to a Z driving device 64 (provided instead of the Z driving circuit 33 in FIG. 4) via a tube 62. The Z drive device 64 is configured by a pump or a valve, and is configured to be able to inject fluid into the tube 62 and suck out liquid from the tube 62.
[0066]
Further, a portion 63 between the tip cover 12 and the optical frame 10 is filled with a transparent fluid.
Further, a filter (not shown) is provided on the front surface of the photodetector 34 of the present embodiment. This filter can pass only wavelengths longer than the wavelength of the laser.
[0067]
Next, the operation of this embodiment will be described.
When it is desired to move the scanning surface 25 in the depth direction with respect to the test portion 13, the tip cover 12 is moved in the Z direction 29 by the Z driving device 64. When the fluid is sent to the intermediate portion 63 through the tube 62 and the hole 61 by the Z driving device 64, the tip cover 12 moves in a direction away from the optical unit 11. On the contrary, when the liquid is sucked out from the intermediate portion 63, the tip cover 12 is moved in a direction approaching the optical unit 11.
[0068]
At this time, since the position of the focal point 23 does not move, it is possible to observe another depth of the test portion 13 by moving the tip cover 12 in the Z direction. At this time, since the position of the tip cover 12 can be measured by measuring the amount of the supplied liquid, it is possible to know which depth image is obtained.
[0069]
Further, here, for example, only the movable mirror 17 is driven by the XY drive circuit 32, the movable mirror 18 is stopped, and instead, the tip cover 12 is slowly driven (moved) by the Z drive device 64. By scanning the cut surface 30 cut into two, the cut surface 30 can be imaged.
[0070]
In the present embodiment, since a filter is provided on the front surface of the photodetector 34, it is possible to observe autofluorescence from the test portion 13.
Moreover, you may observe the fluorescent substance administered beforehand.
[0071]
Further, a spectroscope may be used in place of the photodetector 34. In this case, the wavelength of the fluorescence from the test part 13 can be measured in detail.
Moreover, you may move the front-end | tip cover 12 using the thermal expansion of a fluid instead of taking in and out of a fluid.
A two-photon laser may be used as the light source.
[0072]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
[0073]
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move with respect to the tip of the optical probe 4.
[0074]
Since the focal point 23 of the laser beam is configured to be relatively movable with respect to the depth direction of the test part 13, the surface of the test part 13 having various depths can be observed. A tomographic image can also be obtained.
[0075]
Moreover, the fluorescence from the test part 13 can be observed.
Further, by using a spectroscope, the wavelength of the fluorescence from the test portion 13 can be measured in detail.
[0076]
(Fifth embodiment)
Next, a fifth embodiment of the present invention will be described with reference to FIGS.
Since the present embodiment is different from the first embodiment only in the structure of the distal end portion 9 of the optical probe 4, the description of other portions is omitted.
[0077]
In the present embodiment, the tip cover 12 is configured to be detachably connected to the optical frame 10.
The laser light source used in this embodiment is a wavelength variable laser, and this laser is also driven by the laser drive circuit 31.
In the present embodiment, means for changing the wavelength of the variable wavelength laser is provided without using the Z drive circuit 33.
[0078]
Further, in this embodiment, the front end cover 12 is removed and a front end cover 72 for wide-angle observation provided with, for example, a concave lens portion 71 is attached near the center of the upper surface thereof as shown in FIG.
[0079]
Next, the operation of this embodiment will be described.
As shown in FIG. 9, when it is desired to move the scanning surface 25 in the depth direction with respect to the test portion 13, the wavelength of the variable wavelength laser is changed by the laser driving circuit 31. Thereby, when the wavelength changes, the position of the focal point 23 by the diffraction grating lens 24 changes in the depth direction. Generally, the position of the focal point 23 becomes closer to the diffraction grating lens 24 side as the wavelength becomes longer, and the position of the focal point 23 becomes farther as the wavelength becomes shorter.
[0080]
As a result, the scanning surface 25 of the test portion 13 can be moved in the Z direction 29 for observation.
[0081]
In addition, by changing the voltage and frequency applied to the rotary mirrors 17 and 18 by the XY drive circuit 32, the range of the visual field to be scanned can be changed. Further, when the tip cover 72 for wide-angle observation is attached, the focal point 73 is formed at a farther position as shown in FIG. 10, and a wide range can be scanned.
[0082]
In this case as well, the scanning surface 74 can be scanned by changing the voltage applied to the rotating mirrors 17 and 18. Further, by changing the wavelength of the variable wavelength laser, it is possible to obtain a tomographic image by scanning in the depth direction 75.
[0083]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
[0084]
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move with respect to the tip of the optical probe 4.
Since the focal point 23 or 73 of the laser beam and the test part 13 are configured to be relatively movable with respect to the depth direction of the test part 13, the surface of the test part 13 having various depths is observed. be able to.
[0085]
In addition, since the focal point 23 or 73 is moved using a variable wavelength laser, the configuration of the tip 9 of the optical probe 4 is simpler than that of the first embodiment.
In addition, the scanning range can be changed.
[0086]
In addition, since the tip cover 72 provided with the concave lens portion 71 is made detachable, the field of view range can be greatly changed.
In addition, although the case of the front end cover 72 provided with the concave lens portion 71 has been described, a front end cover provided with a convex lens may be attached so that the observation position in the depth direction can be changed.
[0087]
(Sixth embodiment)
Next, a sixth embodiment of the present invention will be described with reference to FIG.
This embodiment is different from the fifth embodiment only in the tip portion 9 of the optical probe 4, and the description of other portions is omitted.
In the present embodiment, the tip cover 12 is bonded to the optical frame 10.
[0088]
The laser light source of the light source unit 2 used in the present embodiment is a normal laser light source.
In the present embodiment, the Z drive circuit 33 is not used.
In the present embodiment, a birefringent lens 76 is attached to the upper plate 16 of the optical unit 11. The birefringent lens 76 has a focal position that varies depending on the direction of polarization. For example, the focal position becomes the focal point 23 for the polarized light in the direction parallel to the paper surface, and the focal position becomes the focal point 77 for the polarized light in the direction perpendicular to the paper surface.
[0089]
Next, the operation of this embodiment will be described.
The light passing through the birefringent lens 76 has a refractive index that differs depending on the direction of polarization, and thus forms a focal point 77 in addition to the focal point 23. At the time of normal pressing observation, since the focal point 77 is in the deep part of the test part 13, almost no light returns, so that only the image of the scanning surface 25 is obtained.
[0090]
Further, when the optical probe 4 is separated from the test part 13 to some extent, and the surface of the test part 13 is located at a position 78 indicated by a two-dot chain line, there is no object at the focal point 23. While light does not return, light from the focal point 77 returns, so that only an image of the scanning plane 79 is observed.
[0091]
At this time, since the distance from the birefringent lens 76 is different between the focal point 23 and the focal point 77, the scanning surface 79 is wider than the scanning surface 25. Therefore, in the present optical probe 4, two types of scanning ranges can be selected depending on how the optical probe 4 is used.
[0092]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 4, the inside of the body cavity can be observed with a microscope.
Since it is configured so that the axial direction of the optical probe 4 can be observed, it is easier to press against the observation target.
[0093]
Since the transparent window member pressed against the object is provided, the object can be observed in a state where it does not move with respect to the tip of the optical probe 4.
A scanning range can be selected.
[0094]
(Seventh embodiment)
Next, a seventh embodiment of the present invention will be described with reference to FIGS.
An optical scanning probe device 81 according to the seventh embodiment of the present invention shown in FIG. 12 includes a control device 82 having a built-in light emitting means for optical diagnosis and the like, and a base end portion (rear side) of the control device 82. Video signal output from the video signal generating means in the control device 82 and connected to the control device 82 and the optical probe 83 which is inserted in the subject and is incorporated in the subject, and is inserted into the subject. And a monitor 84 for displaying.
[0095]
The control device 82 includes, for example, a white light source 85, and the light from the white light source 85 is collimated by a collimator lens 86, and the parallel light passes through the polarization beam splitter 87 and is parallel to the polarization direction of the polarization beam splitter 87. It becomes linearly polarized light and enters a nipou disc 89 in which a plurality of pinholes 88 that allow spot-like light to pass therethrough are formed.
[0096]
The Nipkow disc 89 is rotated at a constant speed by a motor 90. The light that has passed through the pinhole 88 of the rotated Nipkow disk 89 is collected by the condenser lens 91 and incident on the optical probe 83 side.
[0097]
The optical probe 83 is composed of an elongated transmission fiber 92, and its rear end is fitted to a connector portion 82a provided in the control device 82 and is detachably connected. When the rear end portion is connected to the connector portion 82a, the rear end portion of the transmission fiber 92 is positioned at the position where the light is condensed by the condensing lens 91.
[0098]
The transmission fiber 92 includes a tube 93 and a fiber bundle 94 inserted into the tube 93. As the internal fiber bundle 94, an optical fiber for image transmission having a diameter of about 2 mm is used. This is one pixel corresponding to one pixel, which is a bundle of several tens of thousands, and transmits the light collected and incident by the condensing lens 91 to the tip side.
[0099]
The distal end portion 95 of the optical probe 83 is configured as shown in FIG. In other words, the distal end main body 96 of a hard member is bonded and fixed to the distal end of the tube 93 as an outer tube of the optical probe 83 and the distal end of the fiber bundle 94.
[0100]
A quarter-wave plate 97 and an objective lens 98 are fixed to the tip body 96 so as to face the tip surface of the fiber bundle 94.
[0101]
Then, the linearly polarized light transmitted through the fiber bundle 94 is converted into circularly polarized light through the quarter-wave plate 97, and condensed and irradiated onto the test portion (symmetrical structure) 99 by the objective lens 98. The light focused and irradiated on the test part 99 becomes spot light at the imaging position (focal point) 100.
[0102]
In addition, the light reflected on the test portion 99 side is collected by the objective lens 98, passes through the quarter-wave plate 97, and becomes linearly polarized light having a polarization direction different from that of the forward path by 90 degrees. Return to the Niipou disc 89 via the lens 91. In this case, only light returning from the focal point 100 passes through the pinhole 88, and light from other than the focal point 100 is shielded by the light shielding portion around the pinhole 88.
That is, only the light returning from the focal point 100 enters the polarization beam splitter 87 through a path opposite to the forward path.
[0103]
Then, the light is reflected by the polarization beam splitter 87 and imaged on a charge coupled device (abbreviated as CCD) 102 disposed at the image forming position by the image forming lens 101 facing the polarizing beam splitter 87.
[0104]
The light photoelectrically converted by the CCD 102 is input to a video signal generation circuit in the controller 104, converted into a video signal, output to the monitor 84, and a confocal image is displayed on the display surface of the monitor 84.
A recording device 105 is connected to the controller 104 and can record a video signal.
[0105]
The controller 104 controls the lighting operation of the white light source 85 and the rotation of the motor 90. In addition, a signal from an encoder (not shown) that detects the rotational position of the motor 90 is input, and an image signal generation operation is performed in synchronization with the rotational position of the motor 90.
[0106]
Further, as shown in FIG. 13, the distal end portion 95 is attached so that the proximal end of the transparent distal end cover 111 is fitted, and the distal end cover 111 is movable in the optical axis direction 112 with respect to the distal end body 96. It has become. The tip cover 111 has a convex shape so as to easily fix the tissue.
[0107]
Further, the inside 114 of the tip cover 111 is airtight by the O-ring 113. The tip body 96 is provided with a small pressure sensor 115, which is connected to the controller 104 via the cable 116. By detecting the pressure inside the tip cover 111, the light of the tip cover 111 is detected. The moving position in the axial direction 112 can be detected.
[0108]
Next, the operation of the present embodiment will be described below.
The light emitted from the white light source 85 is converted into parallel light by the collimating lens 86, and only the light having the same polarization direction is transmitted through the polarization beam splitter 87. This light is applied to the upper surface of the Nipkow disc 89.
[0109]
Only the light that has passed through the inner pinhole 88 of the irradiated light is guided to the optical probe 83 by the condensing lens 91, and is condensed at the end of the transmission fiber 92, that is, the rear end surface 94 a of the fiber bundle 94 inside thereof. It propagates through the fiber bundle 94 and is emitted from the tip portion 94b. This illumination light is circularly polarized by the quarter-wave plate 97, then collected by the objective lens 98, and a focal point 100 is formed slightly ahead of the tip cover 111 as a transparent window member.
[0110]
Since the optical probe 83 is used by being pressed against the target tissue 99 at the time of observation as shown in FIG. 13, the focal point 100 is formed inside the tissue. At this time, the reflected light from the tissue returns through the same path and passes through the quarter-wave plate 97, so that the direction of polarization is 90 degrees different from the light emitted from the tip portion 94b of the fiber bundle 94. Then, the light enters the front end portion 94b of the fiber bundle 94.
[0111]
This light propagates again through the fiber bundle 94 and returns in the same optical path, and is focused on the pinhole 88 by the condenser lens 91. At this time, only the light reflected by the focal point 100 on the target tissue 99 due to the confocal effect passes through the pinhole 88, and the reflected light and scattered light from other than the focal point 100 are not focused on the pinhole 88 and thus are removed. The
[0112]
The light that has passed through the pinhole 88 is directed to the polarization beam splitter 87. Here, the polarization plane of the light is reflected by the polarization beam splitter 87 because the polarization plane is 90 degrees different from the light initially transmitted through the polarization beam splitter 87, and is imaged on the CCD 102 by the imaging lens 101. Further, the light reflected by the end faces 94a and 94b of the fiber bundle 94 on the Nipkow disk 89 passes through the polarization beam splitter 87 and is not received by the CCD 102 because the polarization plane remains unchanged.
[0113]
Next, the operation when the Nipkow disc 89 is rotated will be described. In FIG. 14, a plurality of pinholes 88 provided in the Niipou disc 89 are described by distinguishing them by 88a, 88b and the like.
[0114]
When the nipou disc 89 rotates as shown in FIG. 14, the position of the pinhole 88a moves. Along with this, the focal point 120a formed by the light passing through the pinhole 88a and condensed by the condenser lens 91 also moves along a locus 121a as shown in FIG. That is, it moves so as to draw the locus 121a in the direction indicated by the symbol A.
[0115]
When the Nipkow disc 89 further rotates and the focal point 120a deviates from the proximal end portion of the optical probe 3, the focal point formed by the light passing through the next pinhole 88b moves along the same locus 121b.
[0116]
At this time, since the pinhole 88b is located on a radius smaller than that of the pinhole 88a, the locus 121b of the focal point similarly deviates from the locus 121a. By repeating this, the focal point scans the rear end portion of the optical probe 83 two-dimensionally. In this case, the cross-sectional area of the rear end portion 94a of the fiber bundle 94 is configured to be smaller than the range in which the focal point 120a is scanned.
[0117]
Further, the light passing through the pinhole 88a propagates through the fiber bundle 94 and is transmitted to the distal end portion 95, and is irradiated onto the target tissue 99. The return light from the focal point 100 is collected again in the pinhole 88a through the same optical path. The light that passes through the pinhole 88 a forms a focal point 123 on the CCD 102, and the focal point 123 also scans on the CCD 102 in the direction indicated by the symbol B as the Nipkow disc 89 rotates.
[0118]
In addition, since the direction in which light is emitted changes at the distal end portion 95 due to this scanning, the focal point 100 also scans the scanning surface 125 including the focal point 100 of the target tissue 99.
As described above, the focal point 100 scans the target tissue 99 and the information is imaged on the CCD 102.
[0119]
The controller 104 controls the rotation of the Nipkow disc 89 and converts the image signal of the CCD 102 into a video signal, sends this video signal to the monitor 84, and displays a confocal image on the display surface of the monitor 84. Further, it is stored in the recording device 105 as necessary.
[0120]
Further, when it is desired to obtain information on a deeper surface of the target tissue 99, the pressing strength is changed, for example, the tip portion 95 of the probe 83 is strongly pressed against the target tissue 99. At this time, the distal end surface of the distal end main body 96 moves to the right in FIG. 13 with respect to the distal end cover 111 as a window member, and the focal point 100 moves to a deeper portion side of the target tissue 99, and at the moved position. Two-dimensional scanning is performed.
[0121]
At this time, the pressure inside the tip cover 111 increases, and this pressure is detected by the pressure sensor 115. This signal is sent to the controller 104, and from this pressure information, it is possible to know which depth is being observed.
Further, when the tip is released from the state in which the tip of the optical probe 83 is pressed from the target tissue 99, the tip cover 111 returns to the initial position due to the internal pressure.
[0122]
As described above, in this embodiment, the depth information desired to be observed can be obtained by pressing the target tissue 99 with an appropriate strength.
[0123]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 83, the inside of the body cavity can be observed with a microscope.
Since the configuration is such that the axial direction of the optical probe 83 can be observed, it can be more easily pressed against the observation target.
[0124]
Since the Nipou disk 89 is used as the light scanning means, high-speed scanning can be realized.
Since the fiber bundle 94 is used for light transmission, scanning can be performed on the hand side, and the configuration of the tip portion 95 of the optical probe 83 can be simplified.
Moreover, since the window member pressed against the object is convex, it becomes easier to fix the object than in the first embodiment.
[0125]
In addition, since the window member is configured to be movable, it is possible to observe surfaces having different depths of the target tissue.
Further, since the pressure sensor 115 is provided, it is possible to know which depth is being observed.
[0126]
(Eighth embodiment)
Next, an eighth embodiment of the present invention will be described with reference to FIG.
This embodiment is a modification of the distal end portion of the optical probe 83 of the seventh embodiment, and only different portions will be described.
[0127]
The tip portion 95 of the optical probe 83 is as follows. As in the seventh embodiment, a tip main body 96 is bonded and fixed to the tip of the tube 93. The tip body 96 is also fixed to the tip of the fiber bundle 94. A quarter wavelength plate 97 is fixed to the front end surface of the fiber bundle 94. The front end cover 111 serving as a window member is fixed to the front end of the front end main body 96.
[0128]
The objective lens 98 is fixed to a lens frame 130, and the lens frame 130 can move in an axial direction 131 parallel to the optical axis of the objective lens 98. A push-pull rod 132 that can be pushed and pulled is fixed to the lens frame 130. The other end of the push-pull rod 132 is connected to a linear actuator not shown. The linear actuator is connected to the controller 104 in FIG.
[0129]
The position of the focal point 100 can be varied in the depth direction of the target tissue 99 by moving the push-pull rod 132 in the axial direction 131 via this linear motion actuator.
[0130]
Further, the distal end main body 96 is provided with one optical fiber 134 so that the distal end thereof faces the lens frame 130, and this optical fiber 134 is connected to a light source and a detector (not shown) inside the controller 312. .
Then, the light from the light source is transmitted through the optical fiber 134, the reflected light from the lens frame 130 facing the tip surface thereof is detected by the detector, and the objective attached to the lens frame 130 is detected by the detected light intensity. The position of the lens 98 in the axial direction 131 or the position of the focal point 100 can be calculated.
[0131]
Next, the operation of this embodiment will be described.
The operation for obtaining the focal point 100 on the scanning plane 125 is the same as in the seventh embodiment. Therefore, the operation of the mechanism for moving the scanning surface 125 in the axial direction 131 will be described.
[0132]
When the linear actuator is driven by the controller 104, this power is transmitted through the push-pull rod 132 and the lens frame 130 moves in the axial direction. At this time, the focal point 100 moves in the optical axis direction 135 as the objective lens 98 moves. At this time, the scanning surface 125 can also move in the axial direction 135.
[0133]
The optical fiber 134 transmits light from the light source inside the controller 104 to the tip. Here, the light from the fiber 134 is reflected by the portion of the lens frame 130 that faces the tip of the fiber 134, enters the tip surface of the fiber 134 again, and is guided to the detector inside the controller 104.
[0134]
Here, when the lens frame 130 moves, the amount of movement of the lens frame 130 can be accurately known by utilizing the change in the amount of light guided to the detector. This tells you what depth you are observing.
[0135]
In this embodiment, the objective lens 98 is moved. However, the end portion of the fiber bundle 94 and the tip cover 111 as a window member may be moved in the axial direction 131 by the same method.
[0136]
The present embodiment has the following effects.
Since the confocal microscope is configured at the tip of the thin optical probe 83, the inside of the body cavity can be observed with a microscope.
Since the configuration is such that the axial direction of the optical probe 83 can be observed, it can be more easily pressed against the observation target.
[0137]
Since the Niipou disc 89 is used for scanning, high-speed scanning can be realized.
Since the fiber bundle 94 is used for light transmission, scanning can be performed on the hand side, and the configuration of the tip portion 95 of the optical probe 83 can be simplified.
Moreover, since the window member pressed against the object is convex, it becomes easier to fix the object than in the first embodiment.
[0138]
In addition, since the objective lens 98 is configured to be movable, surfaces with different depths of the target tissue can be observed.
[0139]
Further, the position in the depth direction can be determined more accurately than in the seventh embodiment.
Note that embodiments and the like configured by partially combining the above-described embodiments and the like also belong to the present invention.
[0140]
[Appendix]
(0) an optical probe inserted into the body cavity;
A light source for generating light for irradiating the test part with light;
A light transmission means for guiding light from the light source to the tip of the optical probe;
A condensing means for condensing and irradiating the light to be examined;
An optical scanning unit that scans the focal point focused on the test portion side by the condensing unit in a direction orthogonal to the optical axis direction of the condensing unit;
Separating means for separating the return light from the test portion from the light from the light source;
A light detecting means for detecting the separated light;
In the optical scanning probe device comprising:
An optical scanning probe apparatus comprising: a changing unit that can change a position of a focal point focused on the test portion side along an optical axis direction of the focusing unit.
[0141]
(1) a probe inserted into a body cavity;
A light source for generating light for irradiating the test part with light;
An optical fiber for guiding light from the light source to the probe tip;
Condensing means for condensing and irradiating the light to be examined;
Optical scanning means for scanning the focal point collected by the light collecting means;
Separating means for separating the return light from the test part from the optical path of the light from the light source;
A light detecting means for detecting the separated light;
In the optical scanning probe device comprising:
An optical scanning probe apparatus comprising: a focus moving means for continuously moving the focus of the light collected by the light collecting means in the optical axis direction.
[0142]
(2) The optical scanning probe apparatus according to appendix 1, wherein the light source is a laser light source.
(3) The optical scanning probe apparatus according to appendix 1, wherein the focal point moving means moves the focal point in the axial direction of the probe.
(4) The optical scanning probe scanning device according to appendix 1, wherein the optical scanning means is a scanning mirror provided at a probe tip.
[0143]
(5) The optical scanning probe apparatus according to appendix 1, wherein the optical fiber is a bundle fiber, and the optical scanning means scans light incident on the bundle fiber.
(6) The optical scanning probe apparatus according to appendix 5, wherein the optical scanning means has a nippo disk provided with pinholes.
(7) The optical scanning probe apparatus according to appendix 1, wherein the optical scanning probe apparatus forms a confocal optical system.
[0144]
(8) The optical scanning probe apparatus according to appendix 1, wherein the return light from the test part is guided to the outside of the probe through the same optical fiber as the light from the light source.
(9) The optical scanning probe apparatus according to appendix 8, wherein the separating means separates light guided to the outside of the probe by an optical fiber.
(10) The optical scanning probe apparatus according to appendix 1, wherein the light detection apparatus includes a spectroscopic unit.
[0145]
(11) The optical scanning probe apparatus according to appendix 1, wherein means for extracting only fluorescence from the return light is provided.
(12) The optical scanning probe apparatus according to appendix 1, wherein the focus moving means is a variable focus lens.
(13) The optical scanning probe apparatus according to appendix 12, wherein the focus moving means is a variable focus lens that changes a refractive index.
[0146]
(14) The optical scanning probe apparatus according to appendix 12, wherein the focus moving means is a variable focus lens that changes its shape.
(15) The optical scanning probe apparatus according to appendix 12, wherein the focal point moving means is performed by changing the wavelength of the laser light source.
(16) The optical scanning probe apparatus according to appendix 1, wherein the focal point moving means moves the condensing means relative to the probe tip.
[0147]
(17) The optical scanning probe apparatus according to appendix 1, wherein the focal point moving means moves the probe tip with respect to the light collecting means.
(18) The optical scanning probe apparatus according to appendix 1, wherein the focal point moving means moves the tip of the optical fiber in the axial direction.
(19) The optical scanning probe device according to any one of supplementary notes 16, 17, and 18, further comprising a measuring means for measuring the amount of movement.
[0148]
(20) The optical scanning probe apparatus according to any one of appendices 16, 17, and 18, wherein the focal point moving means is driven by an actuator provided at a probe tip.
(21) The optical scanning probe device according to appendix 20, wherein the actuator is a piezoelectric element.
(22) The optical scanning probe apparatus according to appendix 20, wherein the actuator is driven by movement of fluid.
[0149]
(23) The optical scanning probe apparatus according to appendix 19, wherein the focal point moving means is driven by an actuator provided in the vicinity of the rear end of the probe.
(24) The optical scanning probe device according to appendix 23, further comprising a transmission element for transmitting the power of the actuator to the probe tip.
(25) The optical scanning probe apparatus according to appendix 17, wherein the focal point moving means is a moving means that allows the probe tip to move passively by an external force applied to the probe tip.
(26) The optical scanning probe apparatus according to appendix 25, further comprising measurement means for measuring a pressure that changes with the movement.
[0150]
(27) The focus moving means is a second light collecting means detachably provided at the probe tip, and the focus is moved by attaching and detaching the second light collecting means. Optical scanning probe device.
(28) The optical scanning probe apparatus according to appendix 1, wherein the focal point moving unit is configured such that the condensing unit forms a plurality of focal points, and the focal point is moved by selecting the focal point. .
(Background to Appendix 27 and 28)
(Problems of the prior art) In the prior art, the optical system is moved in the axial direction of the optical probe in order to select the objective lens. In such a system, there is a problem that it is difficult to handle in the axial direction of the optical probe and is difficult to handle.
(Purpose) For the purpose of providing an optical scanning probe device capable of easily observing the optical probe in the axial direction, the configurations of appendixes 27 and 28 are adopted.
(Operation) The focal length can be easily changed even in a direct view state.
[0151]
(29) The optical scanning probe apparatus according to appendix 4, wherein the scanning range of the focal point varies depending on the driving frequency and voltage of the scanning mirror.
(30) The optical scanning probe apparatus according to appendix 1, wherein a scanning range of the focal point is changed by the focal point moving means.
(Background to Addendum 29 and 30)
(Problem of the prior art) The prior art has a drawback that there is no means for continuously changing the scanning range of the focal point, and the magnification or scanning range cannot be changed variously.
(Purpose) To provide an optical scanning probe device capable of continuously changing the magnification or scanning range. In order to achieve the purpose, the configurations of Supplementary Notes 29 and 30 are adopted.
(Operation) The scanning range of the focus can be continuously changed.
[0152]
【The invention's effect】
As described above, according to the present invention, there is an effect that an observation image can be obtained along the depth direction by changing the focus position in the optical axis direction with respect to the portion to be examined.
[Brief description of the drawings]
FIG. 1 is a diagram showing an overall configuration of an optical scanning probe apparatus according to a first embodiment of the present invention.
FIG. 2 is a cross-sectional view showing a configuration of a tip portion of an optical probe.
FIG. 3 is a perspective view showing a configuration of an optical unit.
FIG. 4 is a block diagram illustrating a configuration of a control unit.
FIG. 5 is a diagram showing how a focus is scanned when a movable mirror is driven.
FIG. 6 is a cross-sectional view showing a configuration of a distal end portion of an optical probe in a second embodiment of the present invention.
FIG. 7 is a cross-sectional view showing a configuration of a tip portion of an optical probe according to a third embodiment of the present invention.
FIG. 8 is a cross-sectional view showing a configuration of a distal end portion of an optical probe according to a fourth embodiment of the present invention.
FIG. 9 is a cross-sectional view showing a configuration of a distal end portion of an optical probe according to a fifth embodiment of the present invention.
FIG. 10 is a cross-sectional view showing a configuration of a tip portion of an optical probe in a state where a tip cover for wide-angle observation is attached.
FIG. 11 is a cross-sectional view showing a configuration of a tip portion of an optical probe according to a sixth embodiment of the present invention.
FIG. 12 is a diagram showing an overall configuration of an optical scanning probe device according to a seventh embodiment of the present invention.
FIG. 13 is a cross-sectional view showing the configuration of the tip of the optical probe.
FIG. 14 is a diagram for explaining the operation when the Nipkow disc is rotated.
FIG. 15 is a cross-sectional view showing a configuration of a tip portion of an optical probe according to an eighth embodiment of the present invention.
[Explanation of symbols]
1 ... Optical scanning probe device
2 ... Light source
3 Light transmission part
4. Optical probe
5. Control unit
6a, 6b, 6c, 6d ... optical transmission fiber
7 ... 4 terminal coupler
8 ... Tube
9 ... Tip
10 ... Optical frame
11 ... Optical unit
12 ... Tip cover
13 ... test area
14 ... Board
15 ... Spacer
16 ... Upper plate
17, 18 ... Movable mirror (rotating mirror)
19 ... Cable
21, 22 ... Mirror
23 ... Focus
24 ... Diffraction grating lens
25 ... Scanning surface
28: Piezoelectric element
29 ... Depth direction of test part
30 ... cut surface
31 ... Laser drive circuit
32 ... XY drive circuit
33 ... Z drive circuit
34 ... Photo detector
35. Image processing circuit
36 ... Monitor
37 ... Recording device

Claims (3)

An optical probe to be inserted into the body cavity, a light source for generating light for irradiating light to the test portion, a light transmission means for guiding the light from the light source to the tip of the optical probe, and the light to be detected A condensing means for condensing and irradiating the detecting portion; an optical scanning means for scanning the focal point condensed on the test portion side by the condensing means in a direction perpendicular to the optical axis direction of the condensing means; Separating means for separating the return light from the detection part from the light from the light source, and light detection means for detecting the separated light, and the position of the focus focused on the test part side is collected. An optical scanning probe apparatus comprising a changing means for changing along the optical axis direction of the optical means. The optical scanning probe apparatus according to claim 1, wherein the optical scanning unit includes a focal point moving unit that continuously moves a focal point of the light collected by the light condensing unit in an optical axis direction. . The optical scanning probe apparatus according to claim 1, wherein the focal point moving unit moves the focal point in the axial direction of the probe.

Images