JPH08233727A - Scanning-type optical-texture inspecting device - Google Patents

Abstract

PURPOSE: To locate a change of scattering characteristics at human tissue with high spatial resolution, by spatially resolving/detecting a luminous flux passing through the inspected tissue and forming an image of a recorded phase/ amplitude change. CONSTITUTION: Light sources 11a-11c radiate luminous fluxes of different wavelengths λ1 -λ3 modifies in intensity at 20, and a multiplexer element 12 couples the luminous fluxes to a sole emission/beam guide system 15. A scanning device 30 positions the light to a tissue 100 to be inspected. A radiation passing the tissue 100 is spatially resolved/detected by a spatial resolving/detecting device structure. A weak radiation signal passing the tissue 100 is mixed with a lower wavelength by a detecting device 40. A phase shift generated with the light is cast to the tissue 100 and an amplitude of the passing radiation are recorded corresponding to respective wavelengths. A recorded light signal is converted to an electric signal and sent to an evaluation device 60. The device 60 handles a change of the phase and amplitude of wavelength components together with position-dependent data of the device 30 through an image formation process. In this manner, a change of scattering/absorbing characteristics at human tissue can be located with high spatial resolution.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a scanning optical tissue inspection apparatus.

[0002]

BACKGROUND OF THE INVENTION A series of devices or methods are known for examining human tissue for possible tissue abnormalities. X-rays have long been used to perform such examinations. Although this method provides high-contrast images of the skeletal structure of the human body, the image quality achievable during tumor detection is often insufficient to make a reliable diagnosis. In particular, the lack of contrast between different types of tissue to be examined makes such a method only suitable in a very limited situation for a given purpose. Another significant drawback when using X-rays is the ionization effect and the resulting exchange with human tissue. Therefore, there has been a long-felt need for inspection methods or suitable devices that can be realized with non-ionized electromagnetic radiation and that provide image quality sufficient for evaluation.

A device which does not work with X-rays and which is suitable for detecting changes in the absorption coefficient in scattering media is described, for example, in US Pat. No. 4,972,331.
In the phase-modulation spectroscopy method proposed there, radiation having two wavelengths in the near-infrared range is alternately incident on the human tissue to be examined, where the radiation signal is modulated at a high frequency. At the detector side, characteristic radiation dose changes, especially phase shifts occurring in the tissue, are recorded, from which the concentration of the absorbed tissue element, eg the tumor, is inferred.

The device described has several drawbacks. First, the sequential detection of several wavelengths is also carried out due to the use of the selected detector structure, as well as the alternating incidence of electromagnetic radiation of different wavelength ranges, resulting in a measurement. The time will increase. A further problem is that extremely weak optical signals in the high frequency range have to be converted into electrical signals by sensitive detectors. Such a detector must have a wide bandwidth due to the strong signal noise of the HF signal,
Therefore, it is expensive. The electrical signals provided by the detectors are likewise particularly susceptible to high-frequency disturbing electric fields from their respective surroundings. In addition, the structure shown can only be used to determine, for example, the presence of a tumor. No precise indication of tumor location and size within the examined tissue volume is possible.

[0005]

The object of the invention is therefore to ensure that localized changes in the scattering and / or absorption properties of human tissue are localized with the highest possible contrast and high spatial resolution. The present invention is to provide a scanning type optical tissue inspection apparatus. Furthermore, it should allow two-dimensional or three-dimensional image reconstruction from the measured data. In addition, the cost of the equipment is reduced, the measurement time is shortened, and the influence of external disturbance is minimized.

[0006]

This problem is solved by a scanning optical tissue inspection apparatus having the features of the first claim. The scanning optical histology apparatus according to the present invention enables spatially resolved detection of abnormalities in human tissue, eg tumors, including two-dimensional or three-dimensional image reconstruction. A possible application is the early detection of breast cancer. This has the particular result that the instrument cost is significantly lower compared to the known devices, which is due to the construction of the detection device according to the invention. In some embodiments of the detection device, it is possible, for example, to apply a detector with low bandwidth and high sensitivity at a reasonable price.

In addition, two or more different wavelengths are simultaneously coupled into a single light emitting / light guiding system via a multiplexing element, and the detector is appropriately configured. That is, in particular, by combining the demultiplexing means with the corresponding mixing means according to the invention, it is possible to reduce the measuring time by at least one half compared to the prior art mentioned above. In addition, spatial resolution and contrast are improved by image reconstruction according to the convolution principle. For this purpose, the position of the radiation source is fixed and the scanning device is used to measure the scattered light distribution in a wide planar element on the exit side. There are various scanning devices suitable for this.

It has been found to be advantageous to use solid angle selection elements in the scanning device in order to suppress disturbing "effects of external light" during image reconstruction. further,
Depending on the desired design, the device according to the invention is of modular construction, so that the exchange of the individual components is always possible without problems, for example the use of several different mixing and detection devices. Other advantages and details of the scanning optical tissue inspection apparatus according to the present invention will be apparent from the following description of the embodiments with reference to the accompanying drawings.

[0009]

1 is a block connection diagram of a scanning optical tissue inspection apparatus according to the present invention. The device has a modular construction such that the individual components can be interchanged with each other without problems depending on the desired design. The device according to the invention essentially comprises an optical emission device 10, a modulation device 20, a scanning device 30, a detection device 40, a control device 50 and an evaluation device 60. In this case, the optical light emitting device 10 is provided with two or more light sources LQ _i 11a, 11b, 11c that emit radiations having different wavelengths λ _i . Further, for example, Fa. Spectra Di
ode Labs model name SDL7422, SDL243
Laser diodes with 1 etc. can be used, but their laser diode is 670 nm to 9 nm.
Generate a wavelength λ _i of 50 nm. That is, it operates in the range of the (visible) red spectrum to the (invisible) near infrared spectrum. Although three different light sources 11a, 11b, 11c are shown in the block diagram of FIG. 1, it is sometimes necessary to apply more than four different light sources, ie four or more corresponding wavelengths. You can Here, the only decisive factor in choosing the wavelength λ _i to be used is to generate as different absorption characteristics as possible in the human body tissue 100 to be examined.

The light sources 11a, 11b and 11c are modulators 2
The intensity is modulated at a high frequency through 0. To this end, the modulator 20 comprises, for example, commercially available HF oscillators for various light sources, which are Fa. Rohde &
Such as sold by Schwarz under the model name SMG or SMX, but their HF oscillators are not shown in FIG. 1 for the sake of clarity. Or directly based on a digital synthesizer (DDS),
It is also possible to use special oscillators which have at least two HF output terminals in the range 100-500 MHz and are offset by a defined offset Δf, but which are fixedly coupled in terms of phase.

The modulation frequency for the individual light sources 11a, 11b, 11c is advantageously between 100 MHz and 500 MHz, from the high frequency modulation fundamental frequency f plus the defined low frequency modulation offset frequency Δf _i. Become. That is, as a result, for each wavelength λ _i ,
The total modulation frequency f _Gi = f + Δf _i will occur.
The modulation offset frequency Δf _{i of} the individual light sources 11a, 11b, 11c, and therefore the total modulation frequency f _Gi , may be the same depending on the detection device 40 employed, or
It may be different. Some embodiments of the corresponding detection device 40 will be described in more detail with reference to FIGS.

The optical light emitting device 10 includes a light source 11 to be used.
A light source temperature adjusting device (not shown) is further included to operate the a, 11b, and 11c at a stable temperature. This temperature regulator is essential in order to ensure that the phase difference and the amplitude value of the emitted radiation are as stable as possible. The optical light-emitting device 10 further comprises a multiplex element 12, which is shown schematically, and comprises individual light sources 11a, 11
The luminous fluxes emitted from b and 11c are coupled to a single light emitting / light guiding system 15 by this multiplex element. Multiplex element 1 suitable for sequential coupling
2 includes, for example, a "chopper structure" having a chopper wheel which is operated at a prescribed rotational speed to sequentially couple the radiation of the individual light sources 11a, 11b, 11c to the light emitting / light guiding system 15 as described above. Can be used. During sequential multiplexing, the chopper wheels are clocked via the controller 50 at a defined frequency. That is, the light emitting / light guiding system 15
The frequency of the coupling of the individual light sources 11a, 11b, 11c to is controlled by the external controller 50. In addition to such control, the control device 50 that also performs another function as described below is advantageously realized by a software system via a computer.

As an alternative to sequential multiplexing utilizing a chopper structure, a modulated radiation to emission and beam guidance system 1
It is also possible to use the known fiber optic multiplex elements which allow simultaneous coupling to 5, ie parallel coupling and transmission, which is particularly advantageous. Such an optical fiber multiplex element is, for example, marketed by the applicant and is also described in EP 0194612.

As the light emitting / light guiding system 15, it is preferable to use an optical fiber optical waveguide. This optical waveguide has a release optical system 3 for collimating the emitted light beam on the release side.
One. The release optics 31 and / or the light-emission and light-guiding system 15 are preferably associated with a scanning device 30 which performs a routine positioning on the tissue 100 to be examined in the plane of the collimated beam.

Here, it is essential for the function of the scanning device 30, and thus of the entire device according to the invention, to be the tissue 1.
The defined relationship between the dot-like entrance location in 00 and the exit location on the detection side is to generate the spatially resolved detector structure of the scanning device 30. For this purpose, the scanning device 3
Various configurations of 0 are possible.

As shown schematically in FIG. 1, the radiation transmitted by the tissue 100 is detected and directed by a light guiding system 35, eg,
Detection-side coupling optics may be provided for focusing, or coupling, to the fiber optic light guide. Similarly, the control device 50
The scanning device 30, controlled via the, allows synchronous scanning of the tissue 100 to be examined in this scanning structure. That is, the emission side release optical system 31 is connected to the detection side coupling system 3
Always synchronized to 2 and positioned on the same axis. Therefore, in this embodiment, the spatially-resolved detector structure of the scanning device 30 is a detector / detector.
A coupling optical system 32 including a beam guiding system 35 and being positioned synchronously with respect to a collimated light flux.

In a second embodiment of the scanning device 30 which can be seen from FIG. 1 instead of the previous embodiment, instead of synchronous scanning,
The light guide system 15 or the release optical system 31 on the transmitting side is directly arranged at the prescribed position, and detection / detection is performed only on the light receiving side.
The position of the beam guiding system 35 or its coupling optics 32 is modified according to the rules, and the transmitted rays are recorded at different points on a wider lateral planar area. Subsequently, for such a scanning process, the collimated beam can be provided with a plurality of (for example 5-10) light-incident side incident positions.

Finally, in the embodiment of the scanning device described above, on the detection side, instead of a moved point-like spatially resolved detector structure, an optical amplifier is connected in front of the CCD.
It is possible to use a three-dimensional, ie laterally extending, spatially resolved detector structure that includes a camera or CCD array. In this case, the previously connected optical amplifier serves to lower and mix the HF signal to a lower signal frequency. An example of a corresponding scanning device is represented in FIG. It is self-evident that if the "point light source" is held stationary, a CCD array can likewise be used in the spatially resolved detector structure of the scanning device.

On the detector side, the scanning device, ie the spatially-resolved detector structure, should be inspected with the spatially-resolved detector structure in order to record as much as possible of the light rays emerging from the tissue at a defined angle. It is expedient to each have a solid angle selection element with the tissue, so as to suppress the effect of external light from another spatial direction, which interferes with the signal evaluation. A device suitable for this purpose will be described with reference to FIG.
It will be appreciated that such a solid angle selection element is advantageous for all of the previously described scanning device embodiments. In addition, to suppress interfering scattered rays from various directions,
It is possible to operate the scanning device 30 in a confocal configuration.

The weak radiation signal recorded via the scanning device 30 with a defined spatial resolution and transmitted through the tissue 100 passes through the detection light guiding system 35 and finally reaches the detection device 40. Therefore, the weak optical signal that is HF amplitude modulated is mixed with a lower frequency while maintaining the phase information,
Further, in some cases, necessary and appropriate amplification is performed, and the phase shift that has occurred in the irradiated tissue 100 is recorded according to wavelength and the intensity or amplitude of the transmitted radiation is likewise recorded according to wavelength. The recorded optical signals can be converted into suitable electrical signals in the detection device 40 and these electrical signals can be further processed by the evaluation device 60. Serving as the reference for the detection information of the transmitted radiation signal are respectively the signals of the modulator and the optical emitter, namely phase information and amplitude information which, in particular, once applied, change as they penetrate the tissue.

Some possible modifications of the detection device 40 will be described explicitly in FIGS. Tissue 1 after irradiation
00, and changes in the phase and amplitude of the individual wavelength components detected by the detection device 40 finally result in the evaluation device 6
0 for further processing. For this purpose, the evaluation device 60 also makes use of the information of the control device 50 on where the signal was measured via the scanning device 30. Furthermore, the evaluation device 60 carries out the image generation signal processing and the possible subsequent display on the display device, for example the display of a cross-sectional image of the examined tissue.

Improved measurement of the phase, amplitude and DC component of the transmitted or scattered radiation of the collimated light beam by means of the device according to the invention makes it possible to evaluate phase images and modulated images. Appear on the exit side and interpret the measured signal as a diffuse wave diffracted by the tissue structure. in this case,
The phase of the measured value corresponds approximately to the average transit time of the arriving diffused wave at each measurement point, and the amplitude approximately corresponds to the attenuation received by the diffused wave. The diffracted image recorded in the plane by the scanning device 30 is reprocessed for image reconstruction using the tissue model. For example, it stores values representing scattered light distributions, such as distribution time points, asymmetric constants or phase zero crossings, which undergo an iterative reconstruction process in tissue to establish inhomogeneities in absorption and scattering distributions. It represents the starting data above. In the next measurement step, the steps are repeated using the starting data, possibly correcting the data of the previous measurement point.
This iterative method also applies with respect to phase and modulation level, which separates scattering and absorption changes within certain limits. On the output side, the same information about the phase and amplitude changes occurring in the tissue is passed to the evaluation device 60. With regard to this method, the evaluation device 60 uses a specific IC (AS) that enables reconstruction and image processing in a short time.
It is advantageous to use IC).

Various embodiments which may be used for the detection device 40 in the device according to the invention will now be described with reference to FIGS. Examples of these are HF
Mixing means M1, M2 used to mix the signal into a lower frequency signal and usable demultiplexing means D1, D2 which serve for wavelength dependent separation of the signal components of the various light sources LQ _i. , D3 only in the way they are combined.

In this case, the problem as a suitable mixing means is the electric mixing means M1 or the optical mixing means M2.
Together therewith, for example, an optical (optical fiber) demultiplexer D2 or a digital frequency filtering means D3.
As described above, the demultiplexing means operating in parallel can be used in combination. Furthermore, for example, sequential demultiplexing via the known chopper structure D1 is also possible.

The following four combinations (D _i + M _i / M _i + D _i ) of the mixing means and the demultiplexing means will be explained with reference to the schematic block connection diagrams of FIGS. : M2 + D2 FIG. 3: M2 + D3 FIG. 4: D2 + M1 FIG. 5: M1 + D3

A first embodiment of a detection device using the optical mixing means M2 in combination with the optical demultiplexing means D2 is shown in FIG. In this case, in this configuration of the detection device, the modulation offset frequency Δf _i delivered by the modulation device is
Is the same for every wavelength λ _i used.
That is, Δf: = Δf _i .

The HF signals in the MHz range that reach the detector 40 via the scanning device are each modulated with f _G = f + Δf and mixed into a lower frequency by the optical mixing means M2. Their frequencies are in the KHz range of the frequency offset Δf. Optical mixing means M2 suitable for this purpose
As the known acousto-optic mixing means or electro-optic mixing means, for example, an acousto-optic demodulator or an electro-optic demodulator sold by New Focus or A & A can be applied. One example of a suitable acousto-optic modulator is represented in FIG. The high frequency signal f or f / 2 of the modulator with the respective optical mixing means M2 used as reference signal
To operate. What is generated as an output signal of the optical mixing means M2 is a signal having a difference frequency Δf, that is, a frequency in the KHz range. The signals reach the optical demultiplexing means D2, which is then arranged as a known fiber optic demultiplexer. Such a demultiplexer is described, for example, in the applicant's European Patent No. 0194612. The demultiplexing means D2 has a wavelength-specific signal component λ.
₁ , λ ₂ and λ ₃ and their signal components are subsequently detected by the detector DET, which is configured for each wavelength.
1, DET2, DET3. Therefore, the detectors DET1, DET2, DET3 can be used as
For example, it is a reasonably priced NF detector with a narrow band such as a photodiode. The recorded amplitude and phase measurements of the transmitted signal component are finally
In the evaluation stage A of the detection device 40, it is associated with the amplitude and phase of the input signal, for which purpose the frequency offset Δf is used as the reference signal. After performing the phase and amplitude evaluation in the evaluation stage A, the detected evaluation signals are further fed to the evaluation device, which processes them together with the location-dependent information of the scanning device.

A second embodiment of the detector 40 is shown in FIG. In this case, the optical mixing means M2 and the electronic-digital or analog-functioning as the demultiplexing means.
A combination with the frequency filtering means D3 is provided. Through a modulator not shown in FIG. 3, several wavelengths λ _i are given different total modulation frequencies f _Gi = f + Δf _i . That is, the modulation offset frequencies Δf _i of the individual wavelengths are different from each other. Similar to the previously described embodiment of FIG. 2, first, the optical mixing means M2 is similarly operated with the modulation frequency f or f / 2 as the reference signal.
Through the mixing of the HF signal to the lower difference frequency Δf _i . The low-frequency signal components of several wavelengths λ _i with different modulation frequencies Δf _i subsequently reach a single narrow-bandwidth NF detector DET, which is configured, for example, as an avalanche photodiode or a photomultiplier. . Several different wavelengths of the transmitted radiation are separated via the electronic frequency filtering means D3 which is arranged subsequently. That is, in this case, the electronic frequency filtering means D3 is used as the demultiplexing means. The electronic frequency filtering means D3 may be realized by an analog method, a digital method, or a software method, as is well known. As in the previous example,
The various signal components Δf _i transmitted are finally evaluated by the evaluation stage A.
Are associated with the amplitude and phase values of the input signal and are then sent to the evaluation device. The evaluation device further processes that information together with the scanning device location information. The advantage of this embodiment of the detection device 40 is that the measurement time is short,
High sensitivity and low instrument cost due to only one detector required. Moreover, the optical mixing means M2 ensures an optimum suppression of the HF scattered signal.

A third embodiment of the detection device 40 will be described with reference to FIG. In this case, the optical demultiplexing means D2 and the electric mixing means M are used for the purpose of signal processing.
1 and are combined. Therefore, various signal components of several wavelengths are all modulated with the same modulation frequency f _Gi = f + Δf _i . That is, Δf _i for all of the wavelength λ _i:
= Δf. First, different signal components of different wavelengths used are separated according to wavelength in an optical demultiplexing means D2, for example a known fiber optic demultiplexer. Subsequently, the still high-frequency signal reaches the electric mixing means M1. The electric mixing means consists essentially of three separate detectors DET1, DET2, DET3 operated by a modulation frequency f as a reference signal. A problem with suitable detectors DET1, DET2, DET3 that can be used simultaneously for the purpose of mixing HF signals is, for example, Fa. Hamamats
It is a photomultiplier of the type as sold by U under the model name R928. After mixing, the wavelength-separated signals then reach the evaluation stage A as in the previously described embodiment. In the evaluation stage A, the amplitude information and the phase information of the transmitted signal component are associated with the corresponding information of the input signal. The information is finally further processed by the evaluation device in the manner described above.

Finally, the fourth possible for the detection device 40.
The embodiment will be described with reference to FIG. In this case, the electric mixing means M1 is combined with the electronic frequency filtering means D3 as a demultiplexing means. The modulation frequencies f _Gi of some wavelengths are also different from each other in this embodiment. That is, each wavelength λ _i has a total modulation frequency f _Gi = f + Δf _i . First, in the electric mixing means M1 that is modulated with the modulation frequency f, first,
Mixing of the modulation offset frequency range to lower frequencies is performed. For this purpose, as an electric mixing means,
Including the high voltage supply HV, a photomultiplier tube is provided whose amplification is modulated with f. Subsequently, the low frequency signal component Δf _i is separated for each wavelength by the electric frequency filtering means D3. After evaluation stage A,
Again, the phase and amplitude information of the transmitted radiation is compared with the input radiation. Corresponding to the previous embodiment, the information is likewise further processed by the evaluation device.

An optical mixing means suitable for the scanning optical tissue inspection apparatus according to the present invention is shown in FIG. In this case, the acousto-optic modulator takes the form of an ultrasonic standing wave modulator, such as that sold by A & A. The input high frequency signal component is coupled to the optical fiber optical waveguide 201 and the standing wave modulator 200 via the coupling optical system 202, for example, a Grin lens. This modulator is modulated at a high frequency by the ultrasonic transducer 203, which frequency corresponds to one half of the frequency f of the modulator and is offset by each offset frequency with respect to the HF component of the optical signal. ing. The high frequency signal components passing through the standing wave modulator 200 are mixed into the offset frequency Δf _i , and the zero-order diffraction is released from the standing wave modulator 200 via the release optics 205 to provide another optical fiber waveguide. It is further guided through the wave tube 206. The use of such an optical mixing means eliminates the need for converting an extremely weak optical signal in the HF range into a corresponding electrical signal by means of an expensive detector having a high sensitivity and a wide bandwidth. Is significantly reduced. Such sensitive detectors are usually also subject to the effects of HF disturbing electric fields.

FIG. 7 schematically shows another scanning device 300. In this case, the light emitting / light guiding system 1
Only 50 or its release optics 310 can be defined by the scanning device 300 in one plane in a defined manner.
Spatially resolved recordings of transmitted or scattered radiation are performed via a flat stationary detector element 350. For this purpose, a known CCD camera or the like, to which an optical amplifier is connected in front, can be used. The scanning device 300 shown in FIG.
For example, the device according to the invention can be operated to record each resulting scattered light distribution via a planar detector element 350 for a series of discrete incident points. Image measurements are used to perform image reconstruction.

As already suggested in the description of FIG. 1, in order to ensure that the external light is suppressed more sufficiently and thereby improve the measuring accuracy, a stereoscopic element is placed in front of each detector element of the scanning device. It is advantageous to provide a corner selection element. A solid angle selection structure suitable for combination with a planar detector element is shown in FIG.
Is schematically shown. In this case, the tissue 400 to be irradiated,
Two microlens arrays 420a and 420b and a pinhole array 410 are provided between the flat detector element 450 and the flat detector element 450.
Exist in a confocal configuration. Pinhole array 420
Behind is a flat detector element 450, for example a well-known CCD array or CCD camera, in suitable alignment. The effective release angle for each individual detector position depends on the focal length and diameter of each individual microlens and the diameter of each individual pinhole. Further, in the illustrated embodiment, since the diaphragm array is arranged between the microlens array 420 and the tissue 400 to be irradiated on the exit side of the tissue, it is possible to suppress the primary scattered light in the adjacent region. Can be achieved.

A similar solid angle selection effect can also be realized when one or more optical fiber optical waveguides are used as the spatial resolution detector structure. In this case, the core diameter of the optical fiber optical waveguide corresponds to the diameter of one pinhole of the confocal structure described above. At that time, the release angle can be variably set by selecting the jacket material and the jacket thickness of the optical fiber optical waveguide. In such an arrangement, the fiber bundle array or fiber plate is attached directly to the glass plate defining the tissue or boundary to be examined, and the flat detector is aligned with the exit opening of the fiber bundle. There is.

[Brief description of drawings]

FIG. 1 is a block connection diagram of a scanning optical tissue inspection apparatus according to the present invention.

FIG. 2 shows each possible embodiment of the detection device.

FIG. 3 shows each possible embodiment of the detection device.

FIG. 4 shows each possible embodiment of the detection device.

FIG. 5 shows each possible embodiment of the detection device.

FIG. 6 schematically shows an example of a suitable optical mixing means.

FIG. 7 shows another embodiment of a possible scanning device with a laterally extending detector structure.

FIG. 8 shows an embodiment of a solid angle selection element arranged in front of a laterally extending detector structure.

[Explanation of symbols]

10 ... Optical light-emitting device, 11a, 11b, 11c ... Light source,
12 ... Multiplex element, 15 ... Emission / light guide system, 20 ... Modulator, 30 ... Scanning device, 40 ... Detection device, 50 ... Control device, 60 ... Evaluation device, 100 ... Human tissue, M1 ... Electric mixing means, M2 ... Optical mixing means, D1 ...
Chopper structure, D2 ... Optical demultiplexing means, D3
... Frequency filtering means, DET1, DET2, D
ET3 ... Detector, A ... Evaluation stage.

Claims (12)

[Claims] 1. A multiplex element (1) for combining different wavelengths into a single light emitting / light guiding system (15).
An optical light emitting device (10) including 2) for producing coherent radiation having at least two different wavelengths; and a modulator device (20) for intensity modulating the radiation emitted from the optical light emitting device (10) at a high frequency. , The tissue to be examined, as well as positioning the light flux leaving the light-emission and light-guiding system (15) according to the regulations
A scanning device (30) for spatially resolving the transmitted radiation through a spatially resolving detector structure, a mixer means (M1, M2) for mixing high frequency optical signals to lower frequencies, and a wavelength-specific signal component. Demultiplexing means (D1, D2, D3) for separating and /
Or one or more detectors (DET1, DET2, DET3) for detecting the phase and amplitude of the recorded signal, and an evaluation for associating the transmitted signal with the input signal of the signal generated by the optical light-emitting device (10). A detection device (40) having a stage (A) and arranged after the scanning device (30), and an evaluation device for image-forming the signal generated from the evaluation stage (A) of the detection device (40). (60) A scanning optical tissue inspection apparatus comprising: 2. The device according to claim 1, wherein the optical light emitting device (10) includes a temperature adjusting part of the light source (11a, 11b, 11c) in order to operate the light source (11a, 11b, 11c) at a stable temperature. . 3. The device according to claim 1, wherein the optical light-emitting device (10) comprises a fiber optic multiplex element enabling parallel coupling into one light-emitting and light-guiding system (15) of different wavelengths. 4. The modulator (20) provides a high frequency modulation fundamental frequency and a low frequency modulation offset frequency, the low frequency modulation offset frequency being selective for all wavelengths used. The apparatus of claim 1, wherein the total or different modulation frequencies are additively constructed from a high frequency modulation fundamental frequency and a low frequency modulation offset frequency. 5. Device according to claim 4, wherein the modulator device (20) comprises a plurality of HF oscillators which are separately controllable for different wavelengths. 6. The device according to claim 1, wherein the scanning device (30) has a detector structure that extends laterally on the detector side and has a point light source that can be positioned as specified on the light emission side. 7. The scanning device (30) comprises in front of the detector side of each spatially-resolved detector structure a solid angle selection element which allows only the radiation emanating from one point of the tissue according to the rule to reach the detector structure. The device according to claim 1. 8. The detection device (40) comprises on the input side an optical mixing means (M2), the optical fiber demultiplexing means (D2) being arranged after the optical mixing means providing the wavelength dependent signal components to them. 2. The device according to claim 1, wherein the device senses the wavelength corresponding to and sends it to a detector which captures the phase and amplitude information of the recorded signal. 9. The detection device (40) comprises on the input side an optical mixing means (M2), a detector (DET) arranged after the optical mixing means comprising a phase information and an amplitude information of the recorded signal. , And after the detector (DET),
Device according to claim 1, characterized in that electronic frequency filtering means (D3) are arranged which separate the detector signal according to wavelength. 10. The detection device (40) has on the input side a fiber optic demultiplexing means (D2) for demultiplexing high frequency signals according to wavelength and correspondingly wavelength-dividing those signals. Detector for detecting (DET
1, DET2, DET3), wherein the detector simultaneously mixes high frequency signals with lower frequencies to function as an electronic mixing means (M1). 11. The detection device (40) comprises on its input side an electronic mixing means (M1) which mixes the high frequency signal with a lower frequency, the electronic mixing means (M1) being followed by a signal. Frequency filtering means (D) as demultiplexing means for separating the
3. The device according to claim 1, wherein 3) is arranged. 12. The evaluation device (60) is a detection device (40).
1. A display device for carrying out an image forming process of the signal generated from the evaluation stage (A) of claim 1 and including a display device for that purpose.
1. The device according to any one or more of 1.