JPH06165783A - Optical diagnostic device - Google Patents

Abstract

PURPOSE:To obtain an optical diagnostic device capable of safely conducting an operation by detecting a boundary between a normal tissue and a lesion tissue in a vital tissue. CONSTITUTION:In a suction probe 13 which is inserted into a head part 22 for excising a lesion tissue 14, such as a tumor, by a rotating blade and sucking it out, a leading end of an optical fiber 11a introducing a low-interference light is inserted. Low-interference lights generated in SLDs 6a, 6b of a light generation part 5 are emitted from the leading end face of the optical fiber 11a. Reflected lights from the lesion tissue 14 are introduced to an interference light detection part 31, where the reflected lights are made to interface with a reference light varying in light path length. In this manner, the reflected lights are detected in a depth direction. The existing range of the lesion tissue 14 is judged from the signal of the ratio of the reflected lights having two wavelengths.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical diagnostic apparatus for diagnosing a diseased tissue using low coherence light.

[0002]

2. Description of the Related Art In recent years, when diagnosing a living tissue such as the inside of a skull, hematomas coordinated by CT images, a treatment tool is inserted into a tumor through a small perforation, and the hematoma is blindly removed and a tumor biopsy is performed. I was doing an excision.

[0003]

However, since it is blind, there is a risk of accidentally damaging the surrounding normal tissue. Further, JP-A-1-146545 discloses a device for removing hematoma and the like under the observation of a rigid endoscope, but the depth of the surface should be excised when observing the surface portion. Since it is not possible to determine whether or not the diseased tissue is present, there is also a risk of accidentally damaging the surrounding normal tissue. Therefore, there has been a demand for a diagnostic means capable of detecting a boundary in the depth direction between a normal tissue and a diseased tissue in a living tissue without using a biopsy and safely performing an operation.

The present invention has been made in view of the above points, and an object thereof is to provide an optical diagnostic apparatus capable of detecting a boundary between a normal tissue and a diseased tissue in a living tissue and safely performing an operation. There is.

[0005]

Means and Actions for Solving the Problems A treatment instrument to be inserted into a living body and a treatment instrument which is disposed along the treatment instrument and emits measurement light from a position on the distal end side of the treatment instrument and guides reflected light. Light guide means, interference light detection means for interfering the reflected light guided by the light guide means with reference light, and detecting reflected light from the inside of the living body, and internal tissue of the living body from the output signal of the interference light detection means By providing the display means for displaying the information, it is possible to determine the boundary between the tumor part and the normal tissue from the waveform information of the reflected light intensity displayed on the display means. Therefore, it is possible to prevent accidental damage to normal tissue by excision or the like, or to end the operation while leaving the tumor, thus enabling safe operation.

[0006]

Embodiments of the present invention will be described below with reference to the drawings. 1 to 4 relate to a first embodiment of the present invention, FIG. 1 shows a state in which a range of a diseased tissue is examined by the optical diagnostic apparatus of the first embodiment, and FIG. 2 shows a suction probe installed in a patient. FIG. 3 shows a structure of the suction probe, and FIG. 4 shows characteristics of extinction with respect to wavelength.

The optical diagnostic apparatus 1 according to the first embodiment generates light of two wavelengths, detects the light as a signal in which the measurement light and the reference light are interfered with each other, and outputs from the light interference unit 2. Detecting section 3 for performing signal processing on the generated signal and performing signal processing for examining the boundary between the diseased tissue and the normal tissue;
And a display device 4 for displaying a signal output from

The light generating section 5 provided in the light interference section 2 has SLDs 6a and 6b for respectively generating low coherent light having wavelengths λ1 and λ2 different from each other. The light from the SLDs 6a and 6b is guided to one end face of the single mode optical fiber 11a via the lenses 7a and 7b, the dichroic mirror 8, the polarizer 9 and the lens 10, respectively, and for example, the skull 1
2 is emitted from the other end surface (referred to as a front end surface) that is inserted through the suction probe 13 as a treatment tool inserted inside 2 to the side of the lesion tissue 14 such as hematoma. The suction probe 13 excises a lesioned tissue 14 such as a hematoma, and suctions and removes it.

The optical fiber 11a is a coupler 1 on the way.
At 5, it is optically coupled to the other single mode optical fiber 11b. Therefore, the coupler 15 is branched into two and transmitted. The tip side (from the coupler 15) of the optical fiber 11a is wound around a piezoelectric element such as a PZT 16.

A drive signal is applied to the PZT 16 from an oscillator 17a, and the PZT 16 forms a modulator 17 which modulates the transmitted light by vibrating the optical fiber 11a. The frequency of this drive signal is, for example, 5 to 20 KHz. Therefore, the light modulated from the tip end surface of the optical fiber 11a is emitted to the lesioned tissue 14 side.

The suction probe 13 is positioned on the patient's head 22 by a stereotactic brain surgery device 21 as shown in FIG. For example, as shown in FIG. 3, the suction probe 13 is inserted into an outer tube 25 which is inserted into a lesioned tissue 14 through a small hole formed in the skull 12 and a normal tissue 24 therein.

The suction probe 13 has a spiral blade 13a formed over a part of the tip or over the entire length of the suction probe 13. By rotating the suction probe 13, a lesioned tissue 14 is formed.
Can be excised continuously. As shown in FIG. 1, the excised tissue is sucked and stored in the discharge bin 29 through the suction tube 28 connected to the rear end of the suction probe 13 by the suction operation of the suction pump 27.

That is, by rotating the suction probe 13, the diseased tissue 14 can be continuously excised and discharged. Further, the tip end side of the optical fiber 11a is inserted into the suction probe 13, and the tip end surface of the optical fiber 11a is located at the tip (the blade tip) of the suction probe 13 as shown in FIG. 1
It is possible to detect whether or not the tissue to be resected at the tip 3 is inside the diseased tissue 14.

The light reflected on the lesioned tissue 14 side is incident on the tip surface of the optical fiber 11a. This light is a coupler 15
Then, almost half of the light is transferred to the optical fiber 11b and guided to the interference light detector 31 arranged on the rear end face side. In addition, the light reflected by the mirror 32 arranged on the end face of the optical fiber 11b (the reference light branched from the SLDs 6a and 6b side to the optical fiber 11b side by the coupler 15) is also transmitted, and the interference light detection unit is also transmitted. Lead to 31.

That is, the light guided to the interference light detector 31 side is a mixture of the measurement light reflected on the lesion tissue 14 side and the reference light reflected on the mirror 32.

A compensating ring 33 is provided between the tip of the optical fiber 11b and the coupler 15, and the optical path length of the optical fiber 11a for guiding the measurement light and the optical fiber 11b for guiding the reference light are provided. The optical path length of is compensated to be almost equal.

The light emitted from the rear end face of the optical fiber 11b to the interference light detecting portion 31 side is collimated by the lens 34, and the light component polarized by the polarizer 9 is extracted by the analyzer 35, and the half light is further divided. The mirror 36 splits the light into transmitted light and reflected light.

The transmitted light is reflected by the mirror 40, and further, the light reflected by the half mirror 36 passes through a dichroic mirror 37 that splits the transmitted light and reflected light according to the wavelength, and then passes through lenses 38a and 38b, respectively. Photodiodes (abbreviated as PD) 39a and 39b as detectors respectively receive the light.

The light reflected by the half mirror 36 is
The light reflected by the mirror 41 and further transmitted through the half mirror 36 enters the dichroic mirror 37, is branched into transmitted light or reflected light depending on the wavelength, and is received by the PD 39a or 39b via the lens 38a or 38b.

The mirror 41 is attached to an X-stage 42, and the X-stage 42 is moved in a direction X for changing the optical path length by rotating a motor 43. The rotation of the motor 43 is controlled by the computer 44. By changing the optical path length on the reference light side, the measurement light that is almost equal to this optical path length interferes, and PD3
The light is received by 9a or 39b.

That is, by changing the optical path length,
The measurement light (reflected light) reflected at the position in the depth direction of the lesion tissue 14 interferes with the reference light, and by detecting this interference light, the measurement light at each position in the depth direction of the lesion tissue 14 is detected. The reflected light can be detected. The light used for the detection of the interference light has a low coherence, that is, a short interference range, and therefore can be detected with high resolution in the depth direction.

The distance between the half mirror 36 and the mirror 40 and the distance between the half mirror 36 and the mirror 41 are set so as to deviate from each other by at least the interference range (interference distance) of the low coherence light. Interference does not occur between the measurement light component transmitted through 36 and the reflected measurement light component itself.

The signals photoelectrically converted by the PDs 39a and 39b are amplified by the preamplifiers 45a and 45b, respectively, and then applied to the signal input terminals of the lock-in amplifiers 46 of two channels. The drive signal of the oscillator 17a or a signal having the same phase as that of the drive signal of the oscillator 17a is input to the reference signal input terminal of the lock-in amplifier 46 as a reference signal.
A signal component having the same phase as the reference signal in the signal passing through 5b is amplified by, for example, a heterodyne detected frequency,
Further demodulated.

The two-channel signals demodulated by the lock-in amplifier 46 are input to the log amplifier 47, converted into a signal having a ratio of the two signals, amplified, and converted into a digital signal by the A / D converter 48, and then the computer 44. Entered in. The computer 44 controls the rotation of the motor 43 to obtain a signal in the depth direction. The signal of the ratio of the signal intensities obtained by the two wavelengths λ1 and λ2 to the appropriate depth is displayed on the display device 4 with the vertical axis and the depth being the horizontal axis.

FIG. 4 shows characteristics of absorption coefficient of tissue with respect to wavelength. If the wavelength λ1 is, for example, 650 nm and the wavelength λ2 is, for example, 800 nm, both the hemoglobin (HbO2) having oxygen and the hemoglobin (HbR) not having oxygen exhibit almost the same characteristics at the wavelength λ2.
1, the absorption coefficient of hemoglobin (HbO2) with oxygen is small, while hemoglobin without oxygen (HbR)
Has a large absorption coefficient. Therefore, by taking the ratio S1 / S2 of the signals obtained when these lights are used, it can be determined that the normal tissue is present where the ratio signal is large, and conversely the lesion tissue such as hematoma is where the ratio signal is small.

Therefore, the operator can easily judge from the level of the signal displayed on the display device 4 to how far the tissue in front of the suction probe 13 is a lesioned tissue part such as hematoma. According to the above, it can be surely determined whether or not the suction removal can be further continued.

Therefore, it is possible to surely prevent the normal tissue from being accidentally cut and damaged. Further, it is possible to know the boundary in the depth direction between the diseased tissue and the normal tissue without performing detailed biopsy or the like at each depth, so that it is possible to diagnose or treat in a short time. For this reason, it is possible for patients to be cured in a short period of time after surgery because the treatment time by biopsy, etc. can be minimized, and the surgery can be completed in a short time, so that the pain can be greatly reduced. Become.

On the other hand, the operator can complete the operation in a short time by reducing the time required for the biopsy or the like, and the contents to be actually treated can be reduced. It will be possible to significantly reduce the burden of.

FIG. 5 shows a portion of the cutting forceps 51 in a modification of the first embodiment. This modification is the suction probe 13 described above.
Instead, the cutting forceps 51 is used to cut off the diseased tissue in the living tissue.

The cutting forceps 51 has an insertion portion 52 which can be inserted into a living body or the like through a sheath or the like, and a pair of cups 53 having a cutting function in which a sharp blade is formed at the tip of the insertion portion 52. The operation section 54 is formed at the rear end of the insertion section 52 and performs an operation of gripping and opening and closing the cup 53.

Further, in the cutting forceps 51, the optical fiber 11a is inserted into the insertion portion 52 and the operating portion 54, and the tip of the optical fiber 11a is located near the base end of the cup 53. The rear end side of this optical fiber 11a is wound around a PZT 16 as shown in FIG. 1 and coupled with the other optical fiber 11b by a coupler 15.

The other structure is the same as that of the first embodiment.
Also in this modification, the cup 1 is changed from the signal waveform level displayed on the display device before the cutting forceps 51 is actually cut.
It is possible to easily know whether the tissue immediately before or in front of 5 is a normal tissue or a diseased tissue, and to what depth the diseased tissue exists.

FIG. 6 shows the structure of the main part of the second embodiment of the present invention. In the second embodiment, information in the depth direction is obtained with one wavelength. Therefore, the light generator 5 is
It has SLD6a that emits light of one wavelength.
The light 6a is incident on the rear end surface of the optical fiber 11a via the lenses 7a and 10, and is guided to the front end surface on the suction probe side via the coupler 15 and the modulator 17, for example.

The light reflected on the side of the diseased tissue is incident on the front end surface of the optical fiber 11a, and the light transferred to the other optical fiber 11b by the coupler 15 is the PD disposed on the rear end surface thereof.
The light is received by 38a. This PD38a has an optical fiber 1
The reference light reflected by the mirror 41 disposed opposite to the front end surface of 1b via the lens 34 is also incident.

The mirror 41 is mounted on the X-stage 42 and moved in the direction X for changing the optical path length by the stepping motor 43 whose rotation is controlled by the controller 56. The signal photoelectrically converted by the PD 38a is the preamplifier 45.
After being amplified by a, it is input to the lock-in amplifier 46,
Demodulation / amplification is performed.

The output of this lock-in amplifier 46 is A / D
After being converted into a digital signal by the converter 48, it is input to the computer 44. The computer 44 controls the mirror 41 to change the optical path length via the controller 51, and obtains the reflection intensity data at each depth. Then, the display device 4 displays the reflection intensity with respect to the depth.

In the waveform displayed by the display device 4, the wavelength λ1 of the SLD 6a is set to, for example, 650 nm in FIG.
By using the one set to, it is possible to determine that the portion that suddenly becomes smaller with respect to the depth is a lesion tissue such as hematoma.

FIG. 7 shows the essential parts of a third embodiment of the present invention. The third embodiment shows a brain surgery device 59 for removing an obstacle tissue such as a lesion tissue using an endoscope. The brain surgery device 59 has a stereotactic brain surgery device 61 that fixes an optical tube 63 and the like to a head 60, and a sheath 6 that is inserted into an obstacle tissue such as a lesion tissue, the insertion direction of which is determined by the stereotactic brain surgery device 61.
2, an optical tube 63 that is removably inserted in the sheath 62, and an ultrasonic suction device 65 as a treatment instrument that is inserted into the treatment instrument channel of the optical tube 63 so as to advance and retract.
And an adapter 64 that detachably connects the ultrasonic suction device 65 and the optical viewing tube 63, and is connected to the stereotactic brain surgery device 61 to connect the sheath 62, the optical viewing tube 63, the adapter 64, and the ultrasonic suction device 65. And a fixing device 66 that integrally supports the same.

The ultrasonic suction device 65 transmits ultrasonic vibration from a vibrator (not shown) to its tip via a probe, hits the tip against a diseased tissue such as hematoma and crushes it, and pumps it through the lumen of the probe with a pump 90. Aspiration is performed to remove hematomas and the like. The tip side of the optical fiber 11a is inserted into this probe lumen as in the first embodiment. The configuration of the rear end side of the optical fiber 11a is the same as that shown in FIG. 1, for example.

Before removing the hematoma or the like, the signal waveform obtained in the depth direction by the light emitted from the tip end surface of the optical fiber 11a to the lesioned tissue side can be observed to confirm the range where the lesioned tissue exists. Based on the result of this confirmation, hematoma and the like can be surely removed.

The stereotactic brain surgery device 61 has a ring 72 fixed to the operating table 71, the head 60 of the patient is inserted into the ring 72, and, for example, four head fixing screws provided in the ring 72. It is fixed to the stereotactic brain surgery device 61 by 73. The arm 7 is attached to one side of the ring 72 via a positioning device 74.
5, the arm 75 is provided with a sheath holder 76 for holding the sheath 62.

Then, in accordance with the position of the injured part in the brain, the positioning device 74 adjusts in the X, Y and Z directions,
The optimum puncture position of the sheath 62 is set by adjusting the arm 75 and the sheath holder 76 in the α and β directions.

The sheath 62 has a hollow elongated sheath insertion portion and a main body formed at the rear end of the sheath insertion portion. At the rear end of the main body, there is provided a connecting member capable of detachably connecting the optical tube 63 or the mandolin.

Further, a water supply port 78 with a cock communicating with the hollow portion of the sheath insertion portion is provided on the side portion of the main body. The optical tube 63 has a bent eyepiece 63a, and an eyepiece 63b is formed at the rear end of the eyepiece 63a.

The sheath 62 is fixed by a sheath holder 76 provided on the arm 75. The positions of the sheath 62 and the sheath holder 76 are fixed by the fixing device 76. The fixing device 76 has a support tool 77 that integrally supports the sheath 62, the optical tube 63, the adapter 64, and the ultrasonic suction device 65. The support tool 77 and the sheath holding tool 76.
And are fixed with a fixing screw 79. A lower end of a slide device 98 is fixed to the support 77 with a fixing screw 79.

The mandolin is removed after inserting the sheath 62 at the target point. Then, instead of the mandolin, an optical tube 63, an adapter 64 and an ultrasonic suction device 65.
With these assembled, they are inserted into the sheath 62 and connected.

A water supply tube 81 connected to a water supply device (not shown) is connected to the water supply port 78 of the sheath 62, and a light guide cable connected to a light source device (not shown) is connected to a light guide mouthpiece 82 of the optical tube 63. 83 is connected.

Further, the electric cord 8 of the ultrasonic suction device 65
5 is connected to a generator 86 that drives this ultrasonic suction device 65, and the drainage tube 87 is connected to the generator 86.
Are provided so as to be connected to collecting bins 88 for collecting the drainage.

A tube 89 is extended from the collecting bottle 88, and the tube 89 is connected to a drain container (not shown) via a pump 90.

A fixing base 93 of the fixing device 66 is provided on the top of the ring 72 of the stereotaxic apparatus 61, and a supporting base 95 is attached to the fixing base 93 via a slide base 94. A rotary cylinder 96 is rotatably attached to the support base 95, and an arm 97 is scissored in a groove formed in the rotary cylinder 96.

According to this brain surgery device 59, the range of the damaged tissue can be surely judged as in the first embodiment, and therefore, the operation for surely removing the damaged tissue can be performed in a short time and easily.

FIG. 8 shows an optical diagnostic apparatus 1 according to the fourth embodiment of the present invention.
Indicates 01. The optical diagnostic device 101 includes an endoscope 102,
A light source device 103 that supplies illumination light to the endoscope 102.
And an optical fiber 104 inserted through the endoscope 102 is connected, and an optical interference diagnostic device 106 that obtains information for diagnosing a lesion 105 and a signal in the depth direction obtained by the optical interference diagnostic device 106 are provided. It is composed of a display device 107 for displaying.

The endoscope 102 is provided with an elongated and flexible insertion portion 108, a wide operation portion 109 provided at the rear end of the insertion portion 108, and a rear end of the operation portion 109. The eyepiece section 111 and the light guide cable 112 extending from the side of the operation section 109 to the outside.

The operation section 109 is provided with a bending operation mechanism. By operating the bending operation knob 113, the bending section formed at the rear end of the tip 114 of the insertion section 108 can be moved vertically or horizontally. It can be curved in any direction, and the operator can orient the observation window of the tip 114 in a direction suitable for observing the observation site desired to be observed.

A light guide 115 (see FIG. 9) is inserted into the insertion portion 108, the operation portion 109 and the light guide cable 112, and the connector 116 at the proximal end can be detachably attached to the light source device 103. In this mounted state, the illumination light of the lamp inside the light source device 103 is supplied to the end portion of the light guide 115, this illumination light is transmitted, and the other end surface fixed to the illumination window of the tip end portion 114 of the insertion portion 108. Is emitted from the front.

The light guide 115 is divided into two as shown in FIG. 9 on the tip side, for example, inside the insertion portion 108.
By the illumination light emitted from the front end surface of the light guide 115, an optical image of the illuminated observation site such as the lesioned part 105 is formed on its focal plane by the objective lens 121 attached to the observation window adjacent to the illumination window. .

At the position of this focal plane, one end face of the image guide 122 having an image transmitting function is arranged, and the image guide 122 transmits an optical image to the end face on the eyepiece 111 side.

An eyepiece lens (not shown) is attached to the inside of the eyepiece window of the eyepiece portion 111 so as to face the end face of the image guide 122. When the operator brings his eye closer to the eyepiece window, transmission is performed through the eyepiece lens. The enlarged optical image can be observed.

An optical fiber 104, which is inserted from a channel insertion port 124 and which transmits low-coherent light while preserving its polarization plane, is inserted into the channel 123 of the endoscope 102. As shown in FIG. 10, the optical fiber 104 is covered with a heat-shrinkable tube 104a so that it can be inserted into a body cavity, and at least the tip side is fixed with an adhesive. Further, quartz glass or SELFOC lens 104b is arranged at the tip, and is fixed to the inner wall of the heat shrinkable tube 104a with an adhesive. The outer diameter is set to a constant value.

The optical fiber 104 can be detachably attached to the connector receiver of the optical interference diagnostic device 106 at the connector 125 at the rear end thereof, and the optical fiber 104 is attached to the optical fiber 11 in the optical interference diagnostic device 106.
It is connected to the tip surface of a.

The configuration of the optical interference diagnostic device 106 is almost the same as the configuration shown in FIG. That is, in FIG. 6, a polarizer 131 is arranged between the lenses 7a and 10 in the light generating unit 5 and guides the polarized light to the end face of the optical fiber 11a.

Further, the detection section for detecting the interference light between the measurement light and the reference light in the light emitted from the rear end surface of the optical fiber 11b is the lens 1 facing the rear end surface of the optical fiber 11b.
An analyzer 133 is arranged between 32a and 132b to form a Michelson interferometer so that the light component in the direction polarized by the polarizer 131 can be detected by the PD 38a. Other configurations are the same as those in FIG.

Next, an example of use according to the fourth embodiment will be described.
As shown in FIG. 8, the channel insertion port 12 of the endoscope 102
The optical fiber 104 is inserted from No. 4, and the insertion part 108 is made in a state where the lesioned part 105 such as cancer in the stomach 136 can be observed from the oral cavity of the patient 135 through the esophagus.

In this case, the tip surface of the optical fiber 104 is abutted against the lesioned part 105. The wavelength of SLD6a is 700-
Near-infrared light of 1200 nm, coherence length of 10-200
It is assumed that the thickness is 0 μm.

Then, by setting the interference intensity as shown in FIG. 9, the reflected light intensity inside the lesioned part 105 can be obtained according to the setting position of the mirror 41. Mirror 41
11A by changing the setting position of the reflected light intensity and calculating the reflected light intensity as a distribution in the depth direction.
In the case of a tumor formed on the stomach wall as shown in Fig. 11, the signal waveform obtained for this is as shown in Fig. 11 (b).

As shown in FIG. 11B, the reflected light stronger than the boundary between the layers can be obtained.
Tumor infiltration can be seen. With the endoscope 102, the lesioned part 10
From the observation of the surface condition of No. 5, it can be diagnosed as the diseased tissue.

However, it is practically impossible to judge to what extent the diseased tissue exists in the depth direction from the observation of the surface condition. That is, even if the information obtained from the observation of the surface state by the endoscope 102 cannot be used, the information about the internal state can be obtained by obtaining the information inside the surface using the light guided by the optical fiber 104. A more accurate diagnosis can be made.

As shown in FIG. 12, the end of the optical fiber 104 can be fixed from the outlet of the channel 123 of the endoscope 102 to the examined tissue such as the body wall 141.
The umbrella 142 may be provided at the tip of 04.

The umbrella 142 is formed of an elastic material so as to maintain the normally opened state, and when the optical fiber 104 is put in the channel 123, the umbrella 142 is inevitably closed and stored. Then, when the tip of the optical fiber 104 comes out of the channel 123, the umbrella 142 opens.

By pressing the tip of the bone portion of the umbrella 142 against the body wall 141, the body wall 14 at the portion where the tip of the bone portion hits
The tissue of No. 1 is pushed in and it does not shake. In this state, the tip of the optical fiber 104 is also the lesion 1 on the body wall 141.
05 is pressed against a certain portion, and the pressed state is maintained.

Further, as shown in FIG. 13, at least one suction channel 153 is provided in the insertion portion 152 of the endoscope 151, and the distal end surface of the insertion portion 152 is pressed against the body wall 141. The tip surface may be fixed so as to be in close contact with the body wall 141 by performing a suction operation.

In FIG. 13, the fiber adjacent to the light guide 154 indicates the image guide 155, and the objective lens is omitted for simplification.

In this fixed state, when the tip of the optical fiber 104 inserted through the treatment instrument channel 123 is pressed against the lesioned part 105 or the like of the body wall 141, the pressed contact state can be maintained and the depth direction can be maintained. It is possible to obtain a signal without blurring. The mechanism for changing the optical path length is not limited to the one provided on the reference light side, but may be provided on the measurement light side.

[0074]

As described above, according to the present invention, a treatment instrument to be inserted into a living body, a treatment instrument disposed along the treatment instrument, emits measurement light from a position on the distal end side of the treatment instrument, and reflects the measurement light. Light guiding means for guiding light, interference light detecting means for detecting reflected light from the inside of the living body by causing reflected light guided by the light guiding means to interfere with reference light, and output of the interference light detecting means By providing the display means for displaying the information of the internal tissue of the living body from the signal, the boundary between the tumor part and the normal tissue can be judged from the waveform information of the reflected light intensity displayed on the display means. Therefore, it is possible to prevent accidental damage to normal tissue by excision or the like, or to end the operation while leaving the tumor, thus enabling safe operation.

[Brief description of drawings]

FIG. 1 is a configuration diagram of an optical diagnostic apparatus according to a first embodiment of the present invention.

FIG. 2 is a diagram showing a state in which a suction probe is installed on a patient.

FIG. 3 is a configuration diagram of a suction probe.

FIG. 4 is a characteristic diagram showing a characteristic of dimming degree with respect to wavelength.

FIG. 5 is a view showing a cutting forceps portion in a modification of the first embodiment.

FIG. 6 is a configuration diagram of a main part of a second embodiment of the present invention.

FIG. 7 is a configuration diagram of a main part of a third embodiment of the present invention.

FIG. 8 is a diagram showing an entire optical diagnostic apparatus according to a fourth embodiment of the present invention.

FIG. 9 is a diagram showing a configuration of an endoscope and an optical interference diagnostic device.

FIG. 10 is a cross-sectional view showing a configuration of the tip end side of the optical fiber.

FIG. 11 is a diagram showing that a range where a tumor exists in the depth direction can be detected from reflected light.

FIG. 12 is a view showing a state in which an umbrella is provided at the tip of an optical fiber so that it can be fixed to a lesion.

FIG. 13 is a diagram showing a state in which the distal end surface of the insertion portion is fixed to the body wall by suction.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Optical diagnostic device 2 ... Optical interference part 3 ... Detection part 4 ... Display device 5 ... Light generation part 6a, 6b ... SLD 8 ... Dichroic mirror 9 ... Polarizer 11a, 11b ... Optical fiber 12 ... Skull 13 ... Suction probe 14 ... Lesion tissue 15 ... Coupler 17 ... Modulator 21 ... Stereotactic brain surgery device 22 ... Head 24 ... Normal tissue 25 ... Outer tube 27 ... Suction pump 28 ... Suction tube 31 ... Interference light detection unit 35 ... Analyzer 36 ... Herb mirror 37 ... Dichroic mirror 39a, 39b ... PD 40, 41 ... Mirror 43 ... Stepping motor 44 ... Computer 46 ... Lock-in amplifier 47 ... Log amplifier

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[Procedure amendment]

[Submission date] March 11, 1993

[Procedure Amendment 1]

[Document name to be amended] Statement

[Correction target item name] 0036

[Correction method] Change

[Correction content]

The output of this lock-in amplifier 46 is A / D
After being converted into a digital signal by the converter 48, it is input to the computer 44. Computer 44 performs the control for changing the optical path length of the mirror 41 via the controller 5 6 obtains the reflection intensity data at each depth. Then, the display device 4 displays the reflection intensity with respect to the depth.

[Procedure Amendment 2]

[Document name to be amended] Statement

[Name of item to be corrected] 0045

[Correction method] Change

[Correction content]

The sheath 62 is fixed by a sheath holder 76 provided on the arm 75. Further, the sheath 62 and the sheath holder 76 is located is fixed by the fixing device 6 6. The fixing device 6 6 sheath 62, the telescope 63 has a support 77 for supporting integrally the adapter 64 and the ultrasonic aspirator 65, the support 77 and the sheath holder 76
And are fixed with a fixing screw 79. A lower end of a slide device 98 is fixed to the support 77 with a fixing screw 79.

[Procedure 3]

[Document name to be amended] Statement

[Correction target item name] 0055

[Correction method] Change

[Correction content]

A light guide 115 (see FIG. 9) is inserted into the insertion portion 108, the operation portion 109 and the light guide cable 112, and the connector 116 at the proximal end can be detachably attached to the light source device 103. In this mounted state, the illumination light of the lamp inside the light source device 103 is supplied to the end portion of the light guide 115, this illumination light is transmitted, and from the other end surface fixed to the illumination window of the tip portion 114 of the insertion portion 108. It is emitted to the front.

 ─────────────────────────────────────────────────── ─── Continuation of the front page (72) Inventor Kuniaki Kamami 2-43-2, Hatagaya, Shibuya-ku, Tokyo Within Olympus Optical Co., Ltd. (72) Inventor Oka ▲ saki ▼ 2nd birth Hatagaya, Shibuya-ku, Tokyo 43-2 Olympus Optical Co., Ltd. (72) Inventor Tetsumaru Kubota 2-chome, Hatagaya, Shibuya-ku, Tokyo 43-2 Olympus Optical Co., Ltd. (72) Inventor Koji Yasunaga 2 Hatagaya, Shibuya-ku, Tokyo Olympus Optical Industry Co., Ltd. 43-72 (72) Inventor Atsushi Osawa Hatagaya, Shibuya-ku, Tokyo 2-43 Olympus Optical Co., Ltd. (72) Inventor Kaiji Ohashi Hatagaya, Shibuya-ku, Tokyo 2-43-2 Olympus Optical Co., Ltd. (72) Inventor Yoshinao Daimei 2-43-2 Hatagaya, Shibuya-ku, Tokyo Olin Scan Optical Industry Co., Ltd. in

Claims (1)

[Claims] 1. A treatment instrument to be inserted into a living body, a light guide unit which is disposed along the treatment instrument, emits measurement light from a position on the distal end side of the treatment instrument, and guides reflected light. The reflected light guided by the light guide means is caused to interfere with the reference light,
An optical diagnostic apparatus comprising: an interference light detecting unit that detects reflected light from the inside of a living body; and a display unit that displays information on a tissue inside the living body from an output signal of the interference light detecting unit.