WO2003030726A1 - Method for automatically detecting, and treating or sampling object portion such as affected portion and its apparatus - Google Patents

Abstract

A light beam is applied from a light source to an object portion such as an affected portion. From the light reflected from the illuminated object portion, at least two wavelength regions, i.e., the wavelength region specific to the light source and the wavelength region specific to the object portion are selected. The two wavelength regions include the wavelengths at which the intensities of light take on maximum values. The relative intensities of light in the two wavelength regions are quantitatively determined by spectroscopic measuring means. The values obtained by the quantitative determination are outputted in the form of electric signals so as to control means. Thus, an object portion such as an affected portion is quantitatively judged, detected, and treated or sampled.

Description

 Description Method and apparatus for automatically detecting and treating or collecting a target site such as a lesion

 INDUSTRIAL APPLICABILITY The present invention is to detect and detect lesions such as tumors, cancers, atherosclerotic lesions, inflammatory lesions, or lesion sites or useful sites in the medical field, with high precision and accuracy, and quantitatively. The present invention relates to a method and a device for treating or collecting lesions based on information such as destruction, removal, excision of the lesions, administration of drugs to the lesions, or collection of a beneficial site. INDUSTRIAL APPLICABILITY The present invention is extremely effective in the fields of surgery and internal medicine, particularly in the fields of neurosurgery, vascular surgery, cardiology, respiratory surgery, urology and the like, and in the fields of gene therapy, gene research, and drug discovery. Background art

 Conventionally, in the medical field, fluorescent labeling and radioisotope (RI) labeling have been known as methods for identifying and detecting target sites such as lesions and lesions and removing or treating them. In the former fluorescent labeling method, excitatory light is irradiated during treatment to a previously labeled lesion, and the lesion site that is qualitatively recognized as a fluorescent region is visually identified, and the affected lesion tissue is resected or removed. How to treat. The latter isotope labeling is a method of treating lesions that have been detected with a radioactive detection probe while searching for lesions previously labeled with radioisotopes. In addition, as a type of robotic surgical device for automatically removing or treating a detected lesion, a remote surgical robotic device and a high-precision operating robot for position determination (for example, an artificial joint installation port robot) are known. Have been.

However, in such conventional detection and treatment methods, the former method of fluorescence labeling involves detecting tissue during surgery in diagnosing the presence or absence of a lesion to be treated and detecting the boundary between the diseased tissue and normal tissue. Since it was deformed and the quantitative and high-precision evaluation of the lesion was not possible, there was always ambiguity due to visual judgment or qualitative judgment, and no progress could be expected in automated treatment equipment. In addition, the latter radioactive In the isotope labeling method, the spatial resolution of radiation is extremely low, and errors in determining the presence or absence of a lesion are likely to occur.In addition, the place where radioisotopes are used is legally limited and restricted, and the Labeling drugs were also under development and were of little practical use. In other words, conventional fluorescent labeling and radioisotope labeling have the danger of treating and damaging normal tissues and blood vessel areas. Therefore, these labeling methods could not always ensure and guarantee safety. Furthermore, with regard to conventional robotic devices that support surgery, there is a risk that operation errors will always occur with the above-mentioned remote surgery device, and tertiary robots calculated from detected images in CT, MRI, etc. In an artificial joint-installed robot that operates on the basis of the original information, since elastic human tissue is easily deformed by surgical operation, such three-dimensional information may become meaningless. It was limited to immovable objects such as bones that are difficult to deform. In other words, it accurately determines local information such as lesions that move and deform in the operating field, and secures and guarantees quick, reliable, above all, safe and appropriate surgery and medication, and supports surgery freely. It is time for robot surgical equipment to appear.

 An optical diagnostic apparatus disclosed in Japanese Patent Application Laid-Open No. 6-165783 has been proposed as a device capable of detecting such a boundary between a deformed and moving lesion tissue and a normal tissue in an operating field. . This optical diagnostic device inserts the distal end of an optical fiber that guides low-coherence light into a suction probe that is inserted inside the head and cuts and removes diseased tissue such as a tumor with a rotating blade. In the meantime, low coherent light generated by the SLD of the light generating section is emitted from the distal end face of this optical fiber, and light reflected from the affected tissue is guided, and the optical path length is changed by the interference light detecting section. By interfering with the reference light, reflected light in the depth direction is detected, and the range of the presence of the diseased tissue is determined from the signal of the ratio of the reflected light obtained at the two wavelengths. This device detects the boundary between normal tissue and diseased tissue in living tissue, and enables safe surgery.

However, the optical diagnostic apparatus proposed above emits light with low coherence, causes reflected light from the diseased tissue to interfere with reference light, detects reflected light in the depth direction, and detects the range of the presence of the diseased tissue. In order to judge, the reference light generating means is required. Furthermore, the range of the presence of diseased tissue is determined from the signal of the ratio of the wavelength of the reference light and the wavelength of the reflected light whose optical path length is changed Therefore, the qualitative judgment of the diseased tissue was limited, and the detection performance of the boundary between the normal tissue and the diseased tissue was not sufficient. Further, with the proposed optical diagnostic apparatus, it is only possible to determine the distribution of light in the depth direction, and it has been difficult to detect a characteristic characteristic of a lesion.

 Thus, in the present invention, the problem of the conventional diagnostic apparatus is solved by spectroscopy, and the accuracy and accuracy of the localization of the target site such as a lesion is improved, and the target site such as a lesion having high detection performance is automatically detected. It is an object of the present invention to provide a method for detecting and treating or collecting and a device therefor. Disclosure of the invention

 In order to achieve the above object, the technical solution adopted by the present invention is:

A light source irradiates a target site such as a lesion with light, and at least a wavelength range specific to the light source and a wavelength range specific to the target site such as the target lesion in the reflected light emitted from the target site such as the target lesion. In addition, two wavelength regions including the maximum light intensity of each of these two are selected to quantitatively measure the relative light intensity of these two, and the quantitative measurement value is output as an electric signal or a magnetic signal to perform digital control or analysis. A method for automatically detecting, treating, or collecting a target site such as a disease, which is characterized by detecting and treating or collecting while quantitatively determining a target site, such as a lesion, by performing mouth control.

 A light source for irradiating a target site such as a lesion with light; a light intensity measuring unit for separating reflected light emitted from the irradiated diseased tissue into light of at least two wavelengths to measure light intensity of each wavelength; Of the light intensities of these multiple wavelengths, a wavelength range specific to the light source and a wavelength range specific to the target site, such as an irradiated lesion, and two wavelength ranges including the maximum light intensity of each of these are selected. A spectroscopic measuring means for quantitatively measuring the relative light intensity of both, and a digital control or analog converter which converts the quantitative measured value of the relative light intensity into a voltage or a current and outputs it as an electric signal or a magnetic signal. Control means for detecting, treating, or collecting the target site such as a lesion while controlling the amount quantitatively. You.

Also, the light source is a laser light, a light emitting diode, a chemiluminescence, a white light. It is characterized in that it is at least one kind of light emitting means selected from a lamp, a mercury lamp, a xenon lamp and a halogen lamp group.

 Further, the reflected light in the two wavelength ranges that is spectrally selected is one kind of reflected light in a specific wavelength range specific to the light source, and the reflected light is light having a different wavelength from the target part such as a lesion. It is characterized by being light selected from the group consisting of reflected light, light absorption, light emission, fluorescence, and Raman scattering light in a specific wavelength region that is specifically distributed or generated due to the distributed dye.

 Further, when the relative light intensity in the two wavelength ranges quantitatively measured under the treatment or the collection operation does not exceed the threshold value of the light intensity measurement value immediately before the start of the treatment or the collection operation, the treatment or the collection operation is performed. It is characterized in that the control means is digitally controlled or analog controlled so as to continue.

 Further, the present invention is characterized in that a light irradiation is performed on a target portion such as the lesion, and a reflection light from the target portion such as the lesion is received by a probe made of an optical fiber.

 Further, an ultrasonic destruction device, an electric scalpel, a suction device, a laser scalpel, a laser irradiation device, a therapeutic light irradiation device or a biopsy device is incorporated in the probe.

 Further, the probe is incorporated in a surgical catheter. In addition, the present invention is characterized in that light irradiation to a target site such as the lesion and light reception of reflected light from the target site such as the lesion are performed by a lens or a light transmission unit of an interference optical system. The system automatically detects and treats target sites such as the lesions described in 2 to 5. BRIEF DESCRIPTION OF THE FIGURES

 FIG. 1 is a block diagram of a method for automatically detecting and treating or collecting a target site such as a lesion and a systemized block of the apparatus according to the present invention.

Fig. 2 In each of the examples of the probe according to the present invention, Fig. 2 (a) shows an example in which an optical fiber is used as a probe, Fig. 2 (b) shows an example in which a lens or an interference optical system is used as a probe, and Figs. (c) is a diagram showing an example of direct irradiation. Fig. 3 Fig. 3 (a) is a photograph of the unlabeled normal brain tissue under irradiation of a blue light-emitting diode, and Fig. 3 (b) is a confirmed photograph of the brain tumor site labeled with fluorescein Na by specific fluorescence. FIG.

 Fig. 4 Fig. 4 (a) is an analysis of the spectral distribution of normal brain tissue backlit under a blue light-emitting diode using a spectrometer, and Fig. 4 (b) is a brain tumor labeled with fluoride Na. FIG. 5 is an analysis diagram of a spectrum component of a backlit light by a spectrometer. BEST MODE FOR CARRYING OUT THE INVENTION

 Hereinafter, embodiments of a method and apparatus for automatically detecting and treating or collecting a target site such as a lesion according to the present invention will be described in detail with reference to the drawings. Fig. 1 is a systematic block diagram of a method and apparatus for automatically detecting and treating or collecting a target site such as a lesion according to the present invention.Fig. 2 (a) shows an example in which an optical fiber is used as a probe. Fig. 2 (b) shows an example using a lens or an interference optical system as a probe, Fig. 2 (c) shows an example of direct irradiation, and Fig. 3 (a) shows an unlabeled normal brain under irradiation of a blue light-emitting diode. Histological photograph, Fig. 3 (b) shows the same photomicrograph of the specific fluorescence of the brain tumor site labeled with fluorescide Na, and Fig. 4 (a) shows the spectrum of normal brain tissue reflected by blue light-emitting diode. FIG. 4 (b) is an analysis diagram of the spectral distribution of a brain tumor site labeled with Fluorescein Na using a spectrometer for back-lighting.

 In the present invention, as shown in FIG. 1, light is irradiated from a light source 1 to a target site 3 such as a lesion, and at least a wavelength range specific to the light source and at least a portion of the reflected light emitted from the target site 3 such as an irradiated lesion are irradiated. Select two wavelength ranges that are specific to the target site such as a lesion and include the maximum light intensity of each of these, and quantitatively measure the relative light intensity of these two by the spectroscopic measurement means 7. At the same time, by outputting the quantitative measurement value as an electric signal or a magnetic signal and performing digital control or analog control of the control means 8, the target site 3 such as a lesion can be detected and the lesion treatment apparatus 1 can be quantitatively determined. It is characterized by treatment with 0.

Details will be described below. As one embodiment of an apparatus for realizing the method of automatically detecting and treating a target site such as a lesion according to the present invention, as shown in FIG. T JP02 / 09906 A light source 1 that irradiates a target part 3 such as a lesion through a light source, and a reflected light emitted from the target part 3 such as an illuminated lesion through a light transmitting device 4 and at least two wavelengths by a spectroscopic device 5. A light intensity measuring means (optical sensor 1) 6 for dispersing the light into light and measuring the light intensity of each wavelength; Spectroscopic measuring means 7 for selecting two wavelength ranges that are specific wavelength ranges and including the maximum light intensity of each of these two, and quantitatively measuring the relative light intensity of these two, and quantifying the relative light intensity Converts the measured value into a voltage or current and outputs it as an electric or magnetic signal and performs digital control or analog control to detect and treat or collect while quantitatively determining the target site such as a lesion. Control means 8. Light source and irradiation light>

 As the light source 1, at least one kind of light emitting means selected from the group consisting of laser light, light emitting diode, chemiluminescence, white lamp, various lamps, for example, mercury lamp, xenon lamp and halogen lamp is used. By irradiating light from these light sources to target sites such as lesions or lesions that have not been labeled, stained, or unstained, reflected light emitted from the irradiated object is received by the probe, and the received reflected light is optically analyzed. Spectroscopic device 5 such as a dynamic filter, etc., and sharpness is remarkably detected in a strong and clear bright line or a spectral analysis diagram in the spectrum by a spectroscopic measuring means 7 including an optical sensor 1. Select light in two wavelength ranges including the highest intensity. Quantitative measurement is performed using the algorithm of the relative light intensity (light intensity ratio) of both wavelengths. After the quantitative measurement values clearly distinguished by the quantitative measurement are converted into currents and voltages, they are output as electric signals or electromagnetic wave signals, and the control means 8 performs digital control or analog control according to the magnitude. The output is varied by control, and the device is operated under the control to drive the mes II lesion destruction device 10 so that a target site such as a lesion is clearly distinguished and cut or treated.

The detection means and the lesion destruction or collection device are systematized and provided as a treatment or collection device or a robotic operation device. The probe, the optical sensor, and each device constituting the system part can be provided and used as components for the same purpose as the present invention or for another purpose. In addition, the above-mentioned systems and components are used for general resection surgery and laser treatment for cancer including brain tumors, and for atherosclerotic lesions and hearts. It can be used as a device for intravascular surgery such as myocardial infarction and for directly applying drugs to affected parts, lesions, diseased tissues, etc., or as a device for collecting useful parts, and is provided for this purpose.

. As the irradiation light, light having a wavelength in the range of about 200 Onm to about 400 Onm, that is, ultraviolet light, visible light, infrared light, or the like can be used. For example, when a blue light emitting diode is used, the wavelength of the irradiation light is 515 nm. When the irradiation target is labeled with a luminescent substance, for example, a fluorescent labeling agent, Fluoride Na, the irradiation target itself emits light and is also referred to as excitation light.

 Light and Dye>

 In the present invention, light emitted from an object by irradiating the object with light is referred to as back illumination. For example, if the irradiated object is dyed in advance with a red dye, the irradiated object absorbs green / yellow wavelength light and reflects red light (so-called ordinary reflected light). In addition, when the irradiation target is labeled with the above-mentioned fluoroside Na, the irradiation target emits fluorescence having a wavelength of 585 nm under irradiation. Furthermore, when light is irradiated to the pulsating blood vessel, reflected light (in the present invention, this is referred to as Doppler light) having a frequency different from that of the irradiated light is generated due to the Doppler effect. The Doppler light is evaluated as a marker for avoiding vascular damage during surgery. Considering these facts, the reflected light referred to in the present invention means ordinary reflected light, fluorescence, emission, absorption, Doppler light, Brillouin scattered light and Raman scattered light in a specific wavelength range. Can be used as a target for quantitative measurement. Further, in the present invention, a substance capable of producing, under light irradiation, reflection in the above-mentioned specific wavelength region under light irradiation and capable of specifically labeling or staining tissues such as lesions, lesions, affected parts, and the like, is also provided. Substances that can be specifically distributed or can be distributed to tissues can be used.

 Spectroscopic equipment>

 In the present invention, a spectroscopic device capable of discriminating a target wavelength, that is, a specific wavelength region of the irradiation light wavelength and the back illumination light described above can be appropriately selected and used. That is, according to the purpose described above. For example, an optical filter, a spectroscope, an interferometer, etc. can be used.

 Light Sensor>

Existing or commercially available sensors, such as photodiodes, photomultiplier tubes, imaging Tubes, MOS sensors, CCDs, etc. can be processed or modified for use. <Probe and light transmission>

 FIG. 2 shows a light transmitting means or an energy transmitting means for destroying or collecting a target site used in the method and apparatus for automatically detecting, treating, or collecting a target site such as a lesion in the present invention. Fig. 2 shows an embodiment of the probe, which mainly irradiates light to a target site such as a lesion and receives the reflected light, and in Fig. 2 (a), light is transmitted by an optical fiber that enables miniaturization. This is an example in which means 4 is configured. Since the miniaturization enables the incorporation into various treatment devices, it is possible to create and provide devices such as new treatment devices. For example, an ultrasonic destruction device or a laser knife may be incorporated in the probe, and the output may be controlled based on a quantitative measurement value, so that a target site such as a lesion can be automatically broken. Alternatively, a laser-irradiation device may be incorporated into the probe to selectively and photodynamically treat a lesion. In addition, the probe can be incorporated into a surgical catheter such as a blood vessel to selectively treat atheroma in an atherosclerotic lesion by photodynamic treatment or destruction treatment. Irradiation of the object to be irradiated is performed through one or more optical fibers, a lens optical system, a diffraction grating optical system as shown in FIG. 2 (b), or FIG. 2 (c). It can be performed by direct irradiation from a light emitting element or a light irradiation element as shown in FIG. In the case of fluorescent ゃ -Raman light, the reflected light due to light irradiation is transmitted through one or more optical fibers, a lens optical system, a diffraction grating optical system, or directly incident on a light emitting element. Guide to spectroscopic devices and optical sensors. In addition, it can be configured to detect a useful part and efficiently collect it.

 Spectral processing and measurement>

 The concentration of the dye in the target area is measured from the intensity or intensity of the reflected light (normal reflected light, luminescence, fluorescence, Raman scattered light, Doppler light or absorption). However, if absorbance is used, measure from absorbance.

 Definition of light wavelength and its intensity>

The maximum intensity value of the reflected light derived from the dye of the irradiated object is represented by “Iλ0”, and the wavelength thereof is represented by “S0ηm”. In addition, the wavelength; the highest intensity of backlit light originating from a light source other than I 0 PT / JP02 / 09906 Degree value is expressed as “I-s i” and its wavelength is expressed as “λ i-nm”. The light intensity of the background is expressed as “I b”, which includes the optical sensor and noise associated therewith.

 Measurement of light intensity at specific region wavelength>

 The maximum intensity of the light of each wavelength is directly measured for the wavelength of the light emitted from the light source and the back light of the irradiated object. Alternatively, the light intensity is determined based on an evaluation based on a correlation coefficient between a known spectral characteristic of the dye and the light source and the measured spectral characteristic.

 Measurement of the pigment concentration (D) of the irradiated object based on the intensity of the backlit light>

 According to the present invention, the dye concentration D of the irradiated object is calculated as the light intensity by the following equations (1), (2) and (3), and the relative light intensity is measured and calculated from the light intensity. However, in order to minimize errors in these measured values and improve accuracy, the light intensity of the back darland (light intensity in a wavelength range that can be detected outside the wavelength range of the excitation light and reflected light or excitation light non-irradiation) is used. It is desirable to measure the relative light intensity using equation (3) considering “I b”.

 Measured light intensity D = i; i O (1) Relative light speed D = i; i OZi i i (2) Relative light speed D = (i i O— I b) Z (i i i— l b)

 <Control of treatment device>

 Since the measured value of the pigment concentration (D) of the irradiated object described above is obtained as an electric signal or a magnetic signal, these are converted into various energy sources for operating the treatment or sampling device described later, and the size of the energy is measured. The control means varies the output by digital control or analog control in accordance with the control, and operates under the control to drive a scalpel or a lesion destruction device, etc., to clearly identify the target site such as a lesion. Can be removed or treated or harvested. In the present invention, the relative light intensity of the two wavelength ranges quantitatively measured under the treatment operation is a threshold value of the light intensity measurement value immediately before the start of the treatment operation, for example, a zero displacement of the continuously measured light intensity. The control means is digitally controlled or analog controlled so as to continue the treatment or sampling operation within a light intensity range selected within 1Z10000 from the point.

Medical treatment equipment> Existing treatment devices for lesion tissues and lesions, for example, a laser irradiator, a laser scalpel, an ultrasonic destructor, an electric scalpel, an electric scalpel, an electromagnetic irradiator, a shock wave generator, and the like can be used. .

 Example>

 <Marking and differentiation of lesion site>

 Fluorescent labeling agents such as fluorescein Na, which are selectively taken into brain tumor foci and specifically labeled, are injected into the patient's vein in advance, and tumors whose surface has been exposed during surgery for brain tumor excision (Fig. 3 (a )) Was irradiated with excitation light. As a result, only the tumor site showed fluorescence, which could be visually identified (Fig. 3 (b)).

 Measurement of light intensity at the site of labeled lesion>

 The above-mentioned tumor site was locally irradiated with a blue light-emitting diode, reflected light was guided from the irradiated site with an optical fiber, and the spectrum distribution was analyzed with a spectrometer. As a result, in the normal brain tissue around the tumor site, unimodal backlit only at the excitation light wavelength (i = 5 15 nm) specific to the blue light diode was detected (Fig. 4 (a On the other hand, at the tumor site, a bimodal reflection consisting of the excitation light wavelength (s i = 515 nm) and the fluorescence wavelength specific to the fluoride Na (s 0 = 585 nm) is used. Light was detected (Fig. 4 (b)).

 Determination of labeled lesion tissue by calculating relative light intensity>

 Based on the above-mentioned equation (3) relating to relative light intensity, a quantitative measurement value of relative light intensity = 0.477 was obtained as follows.

 D = (I λ 0-I b) / (I A i-I b)

 = 1 3 5/2 8 3

 = 0. 4 7 7

 Note that the above quantitative measurement values were significantly different from those of normal tissues (D = 0), so that the tumor site could be specifically and quantitatively determined. In addition, it was confirmed that if the wavelength of the excitation light was optimized, the accuracy of the relative light intensity could be improved by two digits or more.

As described above, according to the present invention, the fluorescence and the excitation light are decomposed into a wavelength spectrum unique to the excitation light and the fluorescence by the spectroscope or the optical filter, and the respective light intensities are quantified by the optical sensor. Has made it possible to make highly accurate and reliable diagnosis. . By using the fluorescence intensity alone or an algorithm that calculates the ratio of the excitation light to the fluorescence, the relative concentration of the fluorescent labeling substance in the tissue is quantified, and the quantified relative concentration is converted to a voltage output for output. The sampling device can be controlled. As a result, at the site where the labeling drug is distributed, the site can be destroyed or collected according to the concentration, whereas at sites other than the target site, no destruction or collection is performed. Because of this characteristic, it is possible to realize a highly safe and efficient treatment or sampling device with high target site selectivity.

 The embodiments of the present invention have been described above. However, within the scope of the present invention, the types and irradiation forms of light sources, the shapes and types of light transmitting means, the shapes and types of probes, Related components, types of light intensity measuring means such as optical sensors, types of spectroscopic devices such as optical filters, types of spectroscopic measuring means, quantitative measurement of relative light intensity to voltage or current The conversion mode, digital control mode or analog control mode output as an electric signal or a magnetic signal, automatic determination, detection, treatment, and collection of a target site can be appropriately selected.

 The present invention may be embodied in any other forms without departing from its spirit or essential characteristics. Therefore, the above-described embodiment is merely an example in every aspect and should not be interpreted in a limited manner. Industrial applicability

As described above in detail, according to the present invention, a light source irradiates a target site such as a lesion with light, and at least a wavelength range specific to the light source and a target region of the reflected light emitted from the target site such as a target lesion. Select two wavelength ranges that are specific to the target site such as a lesion and include the maximum light intensity of each of the two, quantitatively measure the relative light intensity of these two, and calculate the quantitative measurement value. Digital output or analog control by outputting as an electrical or magnetic signal to quantify light intensity and detect and treat or collect while quantitatively determining the target site such as a lesion during surgery Specific and selective selection of target sites while detecting and diagnosing lesions or lesion sites, such as tumors, atherosclerotic lesions, and inflammatory lesions, with high precision and accuracy, especially, safely and reliably. Performs a treatment and collection, self-a quick and qualified surgery and treatment and Seyaku or taken It can be done dynamically. Furthermore, unlike the conventional method that determines the distribution of light only in the depth direction, a part with beneficial properties from the beginning or a part that has obtained valuable properties due to genetic modification etc. is quantitatively determined with high accuracy. And it is possible to collect efficiently.

 Further, a light source for irradiating the diseased tissue with light, a light intensity measuring means for measuring the light intensity of each wavelength by separating reflected light emitted from the irradiated diseased tissue into light of at least two wavelengths, Of the light intensities of the wavelengths, a wavelength range specific to the light source and a wavelength range specific to the target site, such as an irradiated lesion, are selected, and two wavelength ranges including the maximum light intensity of each of these are selected. A spectroscopic measuring means for quantitatively measuring the relative light intensity of the light, and a digital or analog control by converting the quantitative measured value of the relative light intensity to a voltage or a current and outputting it as an electric signal or a magnetic signal. Control means for detecting and treating a target site such as a lesion while quantitatively determining each part, so that each means can be obtained at low cost by modifying or modifying existing or commercially available equipment. , Surgery or treatment By quantifying light intensity, lesions that are easily deformed inside can be reliably and accurately detected with high precision and accuracy, and differentiated from other sites to ensure appropriate and safe operation, treatment, treatment, administration and collection. This can be done automatically.

 Further, the light source is selected from at least one kind of light emitting means selected from the group consisting of laser light, light emitting diode, chemiluminescence, white lamp, mercury lamp, xenon lamp, and halogen lamp, thereby making it possible to convert existing or commercially available light. By adopting it as a light source, the wavelength of the irradiation light can be within an appropriate range.

 Furthermore, the reflected light in the two wavelength ranges that are spectrally selected is one kind of reflected light in a specific wavelength region specific to the light source, and the reflected light is light having a different wavelength from the reflected light, and is an object such as a lesion. If the light is selected from the group consisting of reflected light, light absorption, luminescence, fluorescence, and Raman scattered light in a specific wavelength region that is specifically distributed due to or distributed in the site, the relative light intensity Bimodal backlighting, whose quantitative measurement value differs greatly between the target site and the other site, is detected, and the target site such as a lesion can be specifically and quantitatively determined.

In addition, if the relative light intensity of the two wavelength ranges quantitatively measured under the treatment operation is within the threshold value of the light intensity measurement value immediately before the start of the treatment operation, the treatment or the collection operation is continued. If the control means is controlled by digital control or analog control so that it continues to operate, the target site can be detected and diagnosed with high precision and accuracy with high reliability and safety, prompt and accurate operation and treatment. And medication or collection can be continued automatically.

 Further, when the target site such as the lesion is irradiated with light and the reflected light from the target site such as the lesion is received by a probe composed of an optical fiber, the lesion probe is an extremely fine optical fiber. It can be integrated into various devices, and can be applied to a wide range of fields such as minimally invasive surgery such as endoscopic treatment and endovascular treatment and gene-related research. In addition, it is structurally robust with no moving parts, and its production cost is low.

 Furthermore, when an ultrasonic destruction device, an electric scalpel, a suction device, a laser scalpel, a laser irradiator, a therapeutic light irradiator or a biopsy device is incorporated in the probe, the probe can detect a target site such as a lesion. The structure can be simplified by combining the function with the therapeutic function, the output can be controlled based on the quantitative measurement value, and the lesion tissue can be automatically destroyed. Lesions can be selectively and photodynamically treated. When a sampling device such as a biopsy device or a suction device is incorporated in the probe, it is possible to determine with high precision a site that has acquired useful characteristics due to genetic modification or the like, and to collect the sample.

 When the probe is incorporated into a surgical catheter, atheroma in an atherosclerotic lesion can be selectively subjected to photodynamic treatment or destructive treatment.

 Further, when the light irradiation to the target site such as the lesion and the reception of the reflected light from the target site such as the lesion are performed by the lens or the light transmission means of the interference optical system, the existing inexpensive light is used. The transmission means can be used and the cost is low.

 As described above, according to the present invention, it is possible to provide a method and apparatus for automatically detecting and treating or collecting a target site having high detection performance by improving the accuracy and precision of localization of the target site such as a lesion. .

Claims

The scope of the claims  1. Light is emitted from the light source to the target site such as a lesion, and at least the wavelength range specific to the light source and the specific Select two wavelength ranges that include the maximum light intensity of each of these two wavelength ranges, quantitatively measure the relative light intensity of these two, and output the quantitative measurement value as an electric signal or a magnetic signal. In addition, by performing digital control or analog control, it is possible to automatically detect and treat target sites such as lesions, which are characterized by quantitatively determining and treating or collecting target sites such as lesions. How to treat or collect.  2. A light source that irradiates a target site such as a lesion with light, a light intensity measuring unit that separates reflected light emitted by the irradiated diseased tissue into light of at least two wavelengths, and measures the light intensity of each wavelength. Of the light intensities of multiple wavelengths, a wavelength range specific to the light source and a wavelength range specific to the target site, such as an irradiated lesion, are selected, and two wavelength ranges including the maximum light intensity of each of these are selected. Spectroscopic measurement means for quantitatively measuring the relative light intensity of the light, and digital control or analog control by converting the quantitative measured value of the relative light intensity to a voltage or a current and outputting it as an electric signal or a magnetic signal. An apparatus for automatically detecting, treating, or collecting a target site such as a lesion, the control device comprising: a control unit for detecting, treating, or collecting the target site such as a lesion by quantitatively determining the target site.  3. The light source is at least one kind of light emitting means selected from the group consisting of laser light, light emitting diode, chemiluminescence, white lamp, mercury lamp, xenon lamp and halogen lamp group. 2. A device that automatically detects and treats or collects target sites such as lesions described in 2.  4. The reflected light in the two wavelength ranges selected by the spectroscopy is one type of reflected light in a specific wavelength region specific to the light source, and the reflected light is light having a different wavelength from the reflected light. The light is selected from the group consisting of reflected light, light absorption, light emission, fluorescence, and Raman scattered light in a specific wavelength region which is specifically distributed due to or distributed in the region. A device that automatically detects and treats or collects the target site such as the lesion described in 2 or 3. 5. The relative light intensity in the two wavelength ranges measured quantitatively during the treatment or sampling operation Alternatively, in a range not exceeding the threshold value of the measured light intensity immediately before starting the sampling operation, the control means is digitally controlled or analog controlled so as to continue the treatment or the sampling operation. An apparatus for automatically detecting, treating, or collecting a target site such as a lesion described in any one of Items 2 to 4.  6. The apparatus according to claim 2, wherein the irradiation of light to the target site such as the lesion and the reception of the reflected light from the target site such as the lesion are performed by a probe comprising an optical fiber. An apparatus for automatically detecting, treating, or collecting a target site such as a lesion described in 5.  7. The probe according to claim 2, wherein an ultrasonic crushing device, an electric scalpel, a suction device, a laser scalpel, a laser irradiator, a therapeutic light irradiator, or a biopsy device is incorporated in the probe. An apparatus for automatically detecting, treating, or collecting a target site such as a lesion described in any one of the above.  8. The apparatus according to claim 2, wherein the probe is incorporated into a surgical catheter, and the target part such as a lesion is automatically detected and treated or collected.  9. The apparatus according to claim 2, wherein the irradiation of light to a target site such as the lesion and the reception of reflected light from the target site such as the lesion are performed by a lens or a light transmission unit of an interference optical system. Automatically detect and treat target sites such as lesions described in