JPH09140666A - Wave length shift type shape measuring diagnostic apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To allow tissue diagnosis or cure monitoring by installing a wave length selecting means for selecting a wave length having a prescribed value of the light intensity to be detected by varying the wave length of the light having a prescribed wave length radiated from a light source in a prescribed range. SOLUTION: A wave length adjustable laser 1 emits a light having a initially defined wave length and the light is introduced in a light processing unit 2, split to two beams by a first beam splitter 6 in which one is introduced to a first shutter 8 through a first mirror 7, and another one directly to a second shutter 9. A subject, for example, a tooth in an oral cavity is put on in front of a CCD camera 3 of a light receiver and is monitored on a displaying means. Any one of the first and the second shutters 8 and 9 is opened on receiving a designation for surface configuration measuring, a beam is radiated to the tooth, the light is detected by a light receiver 3 (camera) and is stored in a memory. The wave length is shifted by the operation of the wave length adjusting means so as to radiate a light shifted by a wave length of a prescribed wave length and it is stored.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION The present invention relates to teeth, gums, jawbones, tongues,
Shape measurement and diagnostic device suitable for shape measurement or functional diagnosis of living body or biomaterials such as cheeks, fillers, extremities, various organs, various implants, etc., especially dental diagnosis and treatment It is suitable for use in.

[0002]

2. Description of the Related Art The prior art will be described using the situation of dental treatment. In the current dental treatment, in order to observe the condition of the patient's teeth, gingiva, and jawbone, treatment is carried out using film information obtained by X-ray photography and visual information obtained by direct visual observation by a dentist. . Also, for dental restoration by shape measurement, mainly model recognition based on impressions made with impression materials is the main form recognition, and shape measurement by part of light is performed from the viewpoint of a restoration device. It does not have functions such as diagnosis and treatment for the living body or biomaterial, and since this shape measurement uses light in a certain wavelength range, it cannot correspond to the optical properties of the living body or biomaterial. There was a problem that the shape had to be measured by applying a covering treatment with an opaque coating material that did not reflect the properties of the above. Further, in the conventional coating process, reflection, scattering of reflected waves, and deterioration of quality due to multiple incidents have to be changed by changing the material depending on color and brightness, and it is very troublesome. There is also a nuclear magnetic resonance method that diagnoses, treats, and repairs by the resonance state of nuclides such as electrons and protons. It was necessary to measure the contrast agent inside or outside the oral cavity using a specific contrast agent. In addition, there were techniques for diagnosing the function of a living body based on the presence or absence of Doppler shift and an oral tissue observation device that simply measures absorption peaks and emission peaks.

[0003]

As described above, it is possible to measure the shape of a living body and a biomaterial from the surface to the deep portion of the living body and the biomaterial by using light and basically not holding the hand. The tissue diagnosis or the treatment monitor of the above could not be comprehensively performed, resulting in a problem.

[0004]

The object of the present invention is to obtain information by X-rays, nuclear magnetic resonance, information that is difficult to obtain from visual information and shape measurement of the surface covering state, or basically for living organisms and biomaterials. And to detect physical and biological characteristics of biological and biomaterials such as their unique static and dynamic resonances with respect to light, absorption, reflection, transmission, opacity, etc. By using the optimum wavelength range, it is possible to detect the optical properties from the surface to the deep part.By measuring the shape from the surface to the deep part, and by observing the changes in the optical properties of all of these sites, tissue diagnosis Alternatively, it is to provide a comprehensive and functional shape measurement, diagnosis, and treatment monitor that enables treatment monitoring.

[0005]

The present invention employs the following technical means in order to achieve the above object. [Means for Claim 1] Applying light having a constant wavelength to the object to be measured,
The light reflected or transmitted by the object to be measured is read by a camera, and a wavelength shift type shape measuring and diagnosing device for observing the surface shape or internal tissue of the object to be measured projects a light of a predetermined wavelength toward the object to be measured. A light source, a light intensity detecting means for detecting the intensity of light reflected by the object to be measured or transmitted through the object to be measured, and a wavelength of light of a predetermined wavelength emitted from the light source is continuously or stepwise within a predetermined range. To
The light intensity detecting means further comprises a wavelength selecting means for selecting a wavelength at which the light intensity has a predetermined value.

[Means for Claim 2] In Claim 1, the wavelength of the light source can be specifically tuned to the absorption wavelength peculiar to the tissue of the living body or the living body material.

[Means of Claim 3] In Claim 1, the wavelength of the light source can be specifically tuned to the tissue-specific resonance wavelength of the living body or the biological material.

[Means of Claim 4] In Claim 1, the wavelength of the light source can be specifically tuned to the tissue-specific transmission wavelength of the living body or the biological material.

[Means of Claim 5] In Claim 1, the wavelength of the light source can be specifically tuned to the tissue-specific co-opaque wavelength of the living body or the biological material.

[Means of Claim 6] In Claim 1,
It is characterized in that the wavelength of the light source can be specifically tuned to the tissue specific reflection wavelength of the living body or the biomaterial.

[Means of Claim 7] In Claim 1,
The light source processing circuit includes an optoelectronic circuit that performs phase modulation.

[Means of Claim 8] In Claim 1,
The light source processing circuit includes an optoelectronic circuit that performs frequency modulation.

[Means of Claim 9] In Claim 1,
The light source processing circuit includes an optoelectronic circuit that performs amplitude modulation.

[Means of Claim 10] In Claim 1, the light source is provided with coherent light.

[Means of Claim 11] In Claim 9, the light source processing circuit is characterized by interference processing.

[Means of Claim 12] In Claim 1, a processing mechanism for extracting a reflected light component from a target object is provided.

[Means of Claim 13] In Claim 1, a processing mechanism for extracting a transmitted light component from a target object is provided.

[Means of Claim 14] Claims 1 to 13 In the shape measuring and diagnosing device, the light irradiating means emits light outside the living body, and emits light generated by the light emitting portion. It is characterized in that it has an optical fiber for guiding it into the body, and makes light emitted from the end of this optical fiber incident on a tissue composed of a living body or a biomaterial.

[Means of Claim 15] In the shape measuring and diagnosing device according to any one of Claims 1 to 13, the image receiving unit receives an image of a biological tissue, and an image transmitting unit that guides the received image to the light receiving unit. It is characterized by being provided.

[Means for Claim 16] The shape measuring and diagnosing device according to any one of claims 1 to 13 comprises an analyzing means for extracting a specific wavelength component from the signal captured by the light receiving section. An image of the extracted wavelength component is displayed on the monitor device.

[Means for Claim 17] The shape measuring and diagnosing device according to claims 1 to 16 is characterized in that the selecting means has an intensity distribution within a predetermined range.

[Means of Claim 18] In the shape measuring and diagnosing device of Claims 1 to 16, the selecting means sets the intensity at a predetermined point.

[Means of Claim 19] In the shape measuring and diagnosing device of Claims 1 to 16, the selecting means sets a shape size within a range of a projection beam intensity equal to or higher than a predetermined value. And

[Means of Claim 20] In the shape measuring and diagnosing device of claims 1 to 16, the selecting means is an amplitude value of the interference fringes.

Basically, the functions of the living body and the living body material can be maintained without any modification. However, various known markers may be positively bonded to the living body tissue or material which does not react to light.

[0026]

The light generated by the variable wavelength light source enters the optical processing device and is projected on the living body and the biological material through various processes. Then, the projected light is reflected and transmitted from the living body and the biological material and reaches the light receiver. By grasping the amplitude, intensity, phase, and wavelength information of the light, individual parameters such as wavelength are changed continuously or intermittently.
The action is to detect physical and biological characteristics such as static and dynamic resonances, absorptions, reflections, transmissions, and opaquenesses of living bodies and biomaterials. In particular, surface information and deep information can be controlled by changing the wavelength.

[0027]

The basic static and dynamic resonances, absorptions, reflections, and transmissions of light with respect to living organisms and biomaterials are basically left untouched. By detecting physical and biological characteristics such as opacity and using its wavelength range, it is possible to detect optical properties from the surface to the deep part, and not only the shape measurement from the surface to the deep part but also all of them. It is possible to perform tissue diagnosis or treatment monitoring by observing changes in the optical properties of the site.

[0028]

DESCRIPTION OF THE PREFERRED EMBODIMENTS Next, a wavelength shift type shape measuring / diagnosing device of the present invention will be described based on the embodiments shown in the drawings.

[Structure of Embodiment] FIG. 1 shows an embodiment, and is a schematic view of a wavelength shift type shape measurement / diagnosis apparatus in surface shape measurement of a beam scanning type and a fringe projection type.

The light source 1 for projecting laser light toward the object to be measured, the light intensity detecting means 4 for detecting the intensity of the light reflected by the object to be measured, and the wavelength of the laser light emitted from the light source are A wavelength varying means for continuously or stepwise changing within a predetermined range, and a wavelength selecting means for selecting a wavelength at which the light intensity detected by the light intensity detecting means has a maximum or minimum or a predetermined intermediate value thereof.

[Operation of Embodiment] Beam Scanning Embodiment When the start switch is turned on, the wavelength tunable laser 1 oscillates the wavelength at the initial set value of 8 microns, and the light enters the optical processing portion 2. And the light is the first beam splitter 6
Each of the separated light beams is guided to the first mirror 7 and the first shutter 8 and the other light beam to the second shutter 9 as they are. As for the axis, the angle of the synthetic beam is 0 by the optical axis changing means.
It is initialized every time.

At this time, as an initial setting, both shutters are
It is closed and in a standby state waiting for opening and closing in synchronization with the measurement start signal. Then, teeth or the like existing in the oral cavity are placed on the front surface of the CCD camera 3 which is a light receiver. Then, the teeth are projected as an image on the display means. In this state, the subject depth and focus are adjusted while monitoring the image.
Further, a predetermined measurement range for obtaining a predetermined light intensity is set. Here, a tooth to be measured is selected on the screen by using a mouse or the like and one point of the tooth is selected. Although there is only one point here, the range may be selected with a square window, a polygon window, or the like.

Then, the command for measuring the surface shape is a keyboard,
Come to the light processing circuit, which is the control part, with a mouse.
In response to the command, either the first shutter 8 or the second shutter 9 is opened and the beam is projected onto the teeth. Then, the beam is projected in the above-mentioned predetermined range.

The projected beam hits the teeth and is reflected and scattered, and the light is detected by the light receiver 3. The received light intensity is stored in the storage device.

Then, the wavelength tunable means operates so as to emit the light shifted from the initial wavelength by a predetermined wavelength. As a result, the wavelength of the wavelength tunable laser is shifted and stored similarly through the same mechanism as described above.

With respect to the wavelength selecting means, the operator selects a wavelength to be used within a certain intensity or a size of a range in which a beam having a certain intensity or more exists, or a difference in intensity between wavelengths is taken, or a known method is used. Enter whether to compare the intensities after various statistical processing using a mouse, keyboard, etc.

Here, according to the above-mentioned setting, one of the measurement points was selected with the beam above the point, and comparison was made based on the difference in the intensity distribution.

Then, the intensity comparison is performed for all the light receiving results of 1, 2, 3, ... The intensity distributions from the 1st wavelength to the Nth wavelength are continuously compared by the comparison means of the calculation part, and the resonance wavelength of the phosphoric acid group of hydroxyapatite which is the main component of the tooth is around 9 microns. The calculation unit detects the wavelength vs. intensity characteristic. Based on this, based on the intensity distribution around 9 microns, the maximum absorption wavelength is selected by the selection unit in the calculation section. The wavelength at this time is the outermost surface detection wavelength. However, the signal intensity to the light intensity detecting means is smaller than the minimum absorption wavelength.

If the intermediate value between the maximum value and the minimum value is selected in time, the detection depth can be controlled, and the signal strength can be controlled in time. If the range is selected from two or more points, the difference between the averages may be used, the difference between the maximum value, the minimum value, the median, the representative value, or the like may be used, or the distribution state thereof may be tested and compared. When the used wavelength is selected within the range of a certain intensity or a beam in which the intensity is higher than the certain intensity, the wavelength having the smallest range is the difference surface detection wavelength.

Then, based on the detected accurate wavelength, the wavelength is passed through the wavelength tunable means through the control section, and as a result, the wavelength of the laser is fixed. The resonance wavelength peak of the phosphate group of apatite contained in enamel and dentin exists near 9 microns, but the wavelength depends on individual differences and the presence or absence of treatment. Scanning becomes necessary.

After the wavelength is determined, the surface shape is measured by the known shape measurement of interference fringes. First, the optical axis changing means 1 for the first mirror and the second mirror
2 and 13 are in a state in which the angle of the motion synthesis beam is set to a predetermined angle and fringes having a predetermined order can be generated and projected. Then, the first shutter 8 and the second shutter 9 are opened, and one light passes through the second mirror and is combined with the other beam by the second beam splitter 11 so that interference fringes are projected on the object and the fringe intensity distribution on the object is Are stored via the light receiver. Then, the surface shape is obtained from the intensity distribution.

[Effects of Embodiment] Here, if the selecting section selects the maximum absorption wavelength of the peak, the outermost surface can be detected,
It is possible to measure the shape or properties of the surface of a living body without adding any hand, and it is possible to obtain effects that cannot be achieved by the coating method. In addition, the detection depth can be controlled by appropriately selecting an intermediate value between the maximum value and the minimum value of the peak, and it is possible to select the wavelength that most prevents deterioration of quality due to reflection, scattering, and multiple incidence of reflected waves. . Further, from the viewpoint of controlling the signal intensity, it is possible to simultaneously measure the living body areas having different optical properties.

[Operation of Embodiment] Stripe projection embodiment FIG. 1 When the start switch is turned on, the wavelength tunable laser 1 oscillates a wavelength at an initial set value of 8 microns, and the light is transmitted to the light processing portion 2. There is. Then, the light is separated into two by the first beam splitter 5, and each of the separated lights is guided to the first mirror 7, one to the first shutter 7, and the other to the second shutter 9 as it is. At this time, the optical axis changing means 12 and 13 of the first mirror and the second mirror are in a state where the angle of the combined beam is set to a predetermined angle and a fringe having a predetermined order can be generated and projected.

At this time, as an initial setting, both shutters are
It is closed and in a standby state waiting for opening and closing in synchronization with the measurement start signal. Then, teeth or the like existing in the oral cavity are placed on the front surface of the CCD camera 3 which is a light receiver. Then, the teeth are projected as an image on the display means. In this state, the subject depth and focus are adjusted while monitoring the image.
Further, a predetermined measurement range for obtaining a predetermined light intensity is set. Here, the tooth to be measured is selected on the screen using a mouse or the like, and the range of the tooth measurement site is selected with a rectangular window or a polygonal window.

Then, the command for measuring the surface shape is a keyboard,
Come to the light processing circuit, which is the control part, with a mouse.
In response to the command, the first shutter 8 and the second shutter 9 are opened, and one light is combined through the second mirror 10 and the other beam by the second beam splitter 11, and interference fringes are projected on the teeth. Then, the interference fringes are projected in the predetermined range.

The projected interference fringes hit the teeth and are reflected and scattered, and the light is detected by the light receiver 3. The received light intensity is stored in the storage device.

Then, the wavelength variable means operates so as to emit the light shifted from the initial wavelength by a predetermined wavelength. As a result, the wavelength of the wavelength tunable laser is shifted and stored similarly through the same mechanism as described above.

Then, with respect to the wavelength selecting means, whether the operator selects the wavelength to be used for the intensity of the amplitude of the interference fringes, or the comparison with the physical quantity corresponding to the frequency and phase components,
Alternatively, whether to compare the intensity of the interference fringes after various known statistical processes is input using a mouse, a keyboard, or the like.

Here, the range of the interference fringes was selected according to the above setting, and the comparison was made based on the difference in the intensity distribution of the amplitude.

Then, the intensity comparison is performed for all the light receiving results of 1, 2, 3, ... The intensity distributions from the first wavelength to the Nth wavelength are continuously compared by the comparison means of the operation part, and the wavelength vs. intensity characteristic is detected by the operation part. Based on this, the wavelength selecting the intensity distribution with the largest amplitude is selected by the selector in the calculation section. The wavelength at this time is the outermost surface detection wavelength.

Here, the detection depth can be controlled by appropriately selecting each wavelength from the maximum value to the minimum value. The intensity distributions of the fringe amplitudes may be compared by the difference between the averages, the maximum value, the minimum value, the median, the representative value, or the like, or the distribution state may be tested and compared.

Then, based on the detected accurate wavelength, the wavelength is passed through the wavelength tunable means through the controller, and as a result, the wavelength of the laser is fixed.

After the wavelength is determined, the surface shape is measured by the known shape measurement of interference fringes. The interference fringes already projected are present on the object, and the fringe intensity distribution is stored via the light receiver. Then, the surface shape is obtained from the intensity distribution.

[Effects of Embodiment] Here, if the selection unit selects the maximum absorption wavelength of the peak, the outermost surface can be detected,
It is possible to measure the shape or properties of the surface of a living body without adding any hand, and it is possible to obtain effects that cannot be achieved by the coating method. In addition, the detection depth can be controlled by appropriately selecting an intermediate value between the maximum value and the minimum value of the peak, and it is possible to select the wavelength that most prevents deterioration of quality due to reflection, scattering, and multiple incidence of reflected waves. . Further, from the viewpoint of controlling the signal intensity, it is possible to simultaneously measure the living body areas having different optical properties.

[Structure of Embodiment] FIG. 2 shows an embodiment and is a schematic diagram of a wavelength-shifting type shape measuring / diagnosing apparatus for internal observation of a living body of a beam scanning type and an interference comparison type.

The light source 1 for projecting laser light toward the object to be measured, the light intensity detecting means 3 for detecting the intensity of the light transmitted by the object to be measured, and the wavelength of the laser light emitted from the light source are A wavelength varying means for continuously or stepwise changing within a predetermined range, and a wavelength selecting means for selecting a wavelength at which the light intensity detected by the light intensity detecting means has a maximum or minimum or a predetermined intermediate value thereof.

[Operation of Embodiment] Beam Scanning Embodiment When the start switch is turned on, the wavelength tunable laser 1 oscillates the wavelength at the initial set value of 8 microns, and the light enters the optical processing portion 2. And the light is the first beam splitter 6
Each of the separated light beams is guided to the first mirror 7 and the first shutter 8 and the other light beam to the second shutter 9 as they are. As for the axis, the angle of the synthetic beam is 0 by the optical axis changing means.
It is initialized every time.

At this time, as an initial setting, both shutters are
It is closed and in a standby state waiting for opening and closing in synchronization with the measurement start signal. Then, teeth existing in the oral cavity are placed at an intermediate position between the first shutter 8 and the beam splitter 11. Then, the teeth are projected as an image on the display means. In this state, the subject depth and focus are adjusted while monitoring the image. At this time, this operation is omitted in the case of a light receiver which is not equipped with an imaging lens. Then, a predetermined measurement range is set. Here, a tooth to be measured is selected on the screen by using a mouse or the like and one point of the tooth is selected. Although there is only one point here, the range may be selected with a square window, a polygon window, or the like.

Then, the command for internal observation is brought to a light processing circuit which is a control part by a keyboard, a mouse and the like. In response to the command, the first shutter 8 opens and a beam is projected on the teeth. Then, the beam is projected in the above-mentioned predetermined range.

The projected beam hits the tooth and is transmitted, and the light is detected by the light receiver 3. The received light intensity is stored in the storage device.

Then, the wavelength variable means operates so as to emit the light shifted from the initial wavelength by the predetermined wavelength. As a result, the wavelength of the wavelength tunable laser is shifted and stored similarly through the same mechanism as described above.

With respect to the wavelength selection means, the operator selects a wavelength to be used within a certain intensity or a size of a range in which a beam having a certain intensity or more exists, or a difference in intensity between wavelengths is taken, or a known method is used. Enter whether to compare the intensities after various statistical processing using a mouse, keyboard, etc.

Here, according to the above-mentioned setting, one of the measurement points was selected with the beam above the point, and comparison was performed based on the difference in the intensity distribution.

Then, the intensity comparison is performed for all the light reception results of 1, 2, 3, ... The intensity distributions from the 1st wavelength to the Nth wavelength are continuously compared by the comparison means of the calculation part, and the resonance wavelength of the phosphoric acid group of hydroxyapatite which is the main component of the tooth is around 9 microns. The calculation unit detects the wavelength vs. intensity characteristic. Based on this, based on the intensity distribution in the vicinity of 9 microns, the maximum absorption wavelength distribution characteristic is selected by the selection unit of the calculation unit.

Here, if the laser oscillation intensity is kept constant and the wavelength is scanned from the maximum value to the minimum value, internal observation depending on the depth direction can be performed. Furthermore, if the signal intensity is controlled in a timely manner according to the wavelength-to-intensity characteristic, internal observation independent of depth is possible. For the comparison of beam intensities, the difference between the averages can be
The difference may be the maximum value, the minimum value, the median, the representative value, or the like, or the distribution state thereof may be tested and compared. When the used wavelength is selected within the range of a certain intensity or a range in which a beam having a certain intensity or more exists, the wavelength having the minimum range is the maximum absorption wavelength.

Then, the wavelength of the laser is fixed or continuously tuned as a result of passing through the wavelength tunable means based on the detected accurate wavelength vs. intensity distribution. The resonance wavelength peak of the phosphate group of apatite contained in enamel and dentin exists near 9 microns, but the wavelength depends on individual differences and the presence or absence of treatment. Scanning becomes necessary. The beam is scanned and, as a result, an intensity distribution corresponding to the internal structure of the tooth appears on the light receiver 3. If the second shutter 9 is opened here, the light that does not pass through the teeth is combined with the light that has passed through the teeth by the beam-by-splitter 11, and the inside can be observed by the combined wave.

[Effects of Embodiment] Based on the wavelength-to-intensity distribution obtained by the above-described means, the oscillation intensity of the laser is kept constant, and if the wavelength scanning from the maximum value to the minimum value is performed, it depends on the depth direction. You can observe inside. Furthermore, if the signal intensity is controlled in a timely manner according to the wavelength-to-intensity characteristic, internal observation that does not depend on the depth can be performed. Moreover, if the wavelength with the highest transmission intensity that does not resonate is selected, internal observation can be performed with a small irradiation amount.
The beam intensity comparison may be a difference in average, a difference in maximum value, minimum value, median, representative value, or the like, or a distribution state thereof may be tested and compared. When the used wavelength is selected within the range of a certain intensity or a range in which a beam having a certain intensity or more exists, the wavelength having the minimum range is the maximum absorption wavelength. Due to these effects, internal observation can be performed with an optimum image.

In this example, the wavelength was varied to selectively control the superficial part and the deep part, but other factors such as resonance,
Absorption, reflection, transmission, and opacity may be used in combination for control.

In this embodiment, a CCD camera is used for the light receiving section, but a solid-state image sensor such as a MOS camera, a CID camera, an infrared camera, an image pickup tube such as a vidicon or a saticon,
Alternatively, another light receiving element such as a diode array may be used.

Although the display portion is provided in this embodiment, it may be provided or not provided.

Although the coherent light source is used as the light source in this embodiment, a non-coherent light source may be provided.

In this embodiment, the method of continuously scanning a single wavelength is presented, but a light source of a plurality of wavelengths may be provided,
A continuous spectrum light source may be provided.

Although the case where no treatment is performed on the living body and the biological material has been listed, the living body may be measured using a monoclonal antibody to which various optical property changing factors are bound,
You may use together various coating materials or contrast agents.

A frequency shifter may be arranged on one or both of the shutters 7 and 8 to control the frequency or phase to control the transmittance and the like.

It is also possible to project one of the two separated lights onto a material and synthesize the scattered reflection or the transmitted light to receive it.

The amplitude of the light source may be changed or modulated statically or dynamically.

The beam may be expanded or contracted for all the optical paths from the light source to the object to be measured. Alternatively, the single beam may be scanned to apparently expand the beam.

In the present embodiment, since the tooth is the object of measurement,
The wavelength tunable range of the light source is about 8 to 12 microns, but the wavelength tunable range of the light source is appropriately adjusted for the living body, and there is no particular wavelength range.

[Brief description of the drawings]

FIG. 1 is a schematic diagram of a reflection type wavelength shift type shape measurement / diagnosis apparatus (Example).

FIG. 2 is a schematic diagram of a transmission type wavelength shift type shape measurement / diagnosis apparatus (Example).

[Explanation of symbols]

 1 wavelength tunable laser 2 light processing part 3 light receiving part 4 light intensity detecting means 5 light processing circuit 6 first beam splitter 7 first mirror 8 first shutter 9 second shutter 10 second mirror 11 second beam splitter 12 first light Axis changing means 13 Second optical axis changing means

Claims (20)

[Claims] 1. A wavelength shift type shape measurement in which light having a constant wavelength is applied to an object to be measured, and light reflected or transmitted by the object to be measured is read by a camera to observe the surface shape or internal tissue of the object to be measured. A light source for projecting light of a predetermined wavelength toward the object to be measured in the diagnostic device, a light intensity detecting means for detecting intensity of light reflected by the object to be measured or transmitted through the object to be measured, and emitted from the light source. The wavelength of the light having a predetermined wavelength is continuously or stepwise changed within a predetermined range, and the light intensity detected by the light intensity detecting means includes a wavelength selecting means for selecting a wavelength having a predetermined value. A wavelength shift type shape measuring / diagnosing device characterized by: 2. The shape measuring / diagnosing apparatus according to claim 1, wherein the wavelength of the light source can be specifically tuned to the absorption wavelength peculiar to the tissue of the living body or the biomaterial. 3. The shape measuring and diagnosing device according to claim 1, wherein the wavelength of the light source can be specifically tuned to the tissue-specific resonance wavelength of a living body or a biomaterial. 4. The shape measuring and diagnosing device according to claim 1, wherein the wavelength of the light source can be specifically tuned to the tissue-specific transmission wavelength of a living body or a biomaterial. 5. The shape measuring / diagnosing device according to claim 1, wherein the wavelength of the light source can be specifically tuned to the tissue-specific co-opaque wavelength of the living body or the biomaterial. 6. The shape measuring and diagnosing device according to claim 1, wherein the wavelength of the light source can be specifically tuned to the tissue specific reflection wavelength of a living body or a biomaterial. 7. The shape measuring and diagnosing apparatus according to claim 1, wherein the light source processing circuit includes an optoelectronic circuit for performing phase modulation. 8. The shape measuring and diagnosing device according to claim 1, wherein the light source processing circuit includes an optoelectronic circuit for performing frequency modulation. 9. The shape measuring and diagnosing apparatus according to claim 1, wherein the light source processing circuit includes an optoelectronic circuit for performing amplitude modulation. 10. The shape measuring and diagnosing device according to claim 1, wherein the light source includes coherent light. 11. The shape measuring and diagnosing device according to claim 10, wherein the light source processing circuit is also capable of projecting interference fringes. 12. The shape measuring / diagnosing apparatus according to claim 1, further comprising a processing mechanism for extracting a reflected light component from the target object. 13. The shape measurement / diagnosis apparatus according to claim 1, further comprising a processing mechanism for extracting a transmitted light component from the target object. 14. The shape measuring and diagnosing device according to claim 1, wherein the light irradiating means comprises a light emitting section for generating light outside the living body, and an optical fiber for guiding the light generated by the light emitting section into the living body. The shape measuring and diagnosing device, characterized in that light emitted from the end of the optical fiber is incident on a living body or a tissue composed of a biological material. 15. The shape measuring / diagnosing device according to claim 1, wherein the image receiving unit receives an image of a biological tissue,
The shape measurement / diagnosis apparatus, further comprising: an image receiving transmission unit that guides the received image to the light receiving unit. 16. The shape measuring and diagnosing device according to claim 1, further comprising an analyzing means for extracting a specific wavelength component from a signal captured by the light receiving section, and the wavelength component extracted by the analyzing means. The shape measurement / diagnosis device, wherein the image of the above is displayed on the monitor device. 17. The shape measuring / diagnosing device according to any one of claims 1 to 16, wherein the selecting means has an intensity distribution within a predetermined range. 18. The shape measuring and diagnosing device according to any one of claims 1 to 16, wherein the selecting means sets the intensity at a predetermined point. 19. The shape measuring and diagnosing device according to any one of claims 1 to 16, wherein the selecting means sets the size of the shape within a range of a projection beam intensity equal to or higher than a predetermined value. 20. The shape measuring and diagnosing device according to any one of claims 1 to 16, wherein the selecting means is an amplitude value of an interference fringe.