RU2138192C1 - Method of identification of tissue type and apparatus for method embodiment - Google Patents

Abstract

FIELD: medicine; applicable in diagnoses, both, of external surfaces of skin, and also of internal organs, for instance, in diagnosis of carcinoma of uterine cervix. SUBSTANCE: device for embodiment of claimed method includes probe with shape suitable for contact with tissue. Probe has devices for acting on tissue with numerous various stimulants such as electrical, light, heat, sound, magnetic, and determination of physical response actions to said stimulants. Probe is connected to analog unit which serves as buffer for signals between probe and processor. To classify tissues, processor processes responses in definite combinations, and then, compares classified tissue with catalogue of expected types of tissues to identify the examined tissue. Processing of obtained data is carried out in real time, and type of tissue is indicated to operator. EFFECT: higher efficiency of use for diagnosis of a large number of tissue types and carcinoma in points difficult to access. 23 cl, 20 dwg

Description

 The invention relates to a method and apparatus for diagnosing various types of tissues, including cancerous, precancerous, pathological, as well as tissues in an intermediate state.

 Diagnosis of various types of tissues is carried out by a series of measurements of their physical properties.

 The present invention relates, in particular, to the diagnosis of tissue types such as the outer surface of the skin, as well as those that can be examined using endoscopic agents that allow penetration directly into the body.

 A special application of this invention is associated with the diagnosis of cervical cancer.

 Early detection of a cancerous or precancerous state of the tissue is very important for successful treatment. Currently used diagnostic equipment has low accuracy, depends on operator errors and is time consuming.

 A good example of this is the method for diagnosing the cervix by examining a Pap test (Pap Smear test).

 Radiodiagnosis, which can also be used to diagnose advanced types of cancer, is associated with unhealthy radiation.

 A positive result obtained using the Pap test is usually accompanied by a visual examination using a colposcope, which gives an enlarged view of the cervix. Assessment of suspected areas of the cervix is carried out by an experienced doctor who gives a subjective conclusion on the state of the tissue under study.

 The cervix consists of many types of tissue, some of which are very similar and have similar visual and structural characteristics. This significantly complicates the clinical diagnosis and leads to errors.

 The aforementioned subjective error plays a large role in the determination and treatment of other localizations of pre-tumor and tumor formations, such as, for example, melanoma.

 To distinguish cancer from normal tissue, work was done to create methods and devices based on measuring the physical characteristics of the tissue. The operation of these devices is based on measuring the electrical parameters of the skin or tissue. However, such electrical measurements do not allow obtaining the information necessary for effective diagnostics.

 US Pat. No. 4,537,203 describes a device for detecting abnormal cells having two electrodes connected to a portion of the body.

 Two voltages at different frequencies are applied to two electrodes. The value of capacitance, measured at two frequencies, serves as an indicator of the presence of abnormal cells.

 US Pat. No. 4,955,383 describes a method and apparatus for determining the presence or absence of tissue pathology.

 Skin surface potentials are measured using an electrode matrix. US Pat. No. 5,143,079 describes devices for detecting a tissue tumor. The devices contain in their composition means for determining the dielectric constant of living human tissue. The specific surface resistance depends on the dielectric constant and tissue conductivity. Resistance changes are associated with tissue heterogeneity.

 It is also known to measure the physical characteristics of tissue by optical methods. An example is the device described in US Pat. No. 5,036,853. This device is designed to recognize cervical tissue in which physiological changes due to a tumor or pre-tumor state are expected. In the described device to prevent incorrect measurements, it is required to ensure the correct position of the probe relative to the surface of the cervix. As follows from the patent, the device does not provide means to guarantee the correct installation of the probe.

 A known method for diagnosing a precancerous or cancerous state of tissue, including exposure to tissue with energy stimuli, determining tissue responses to each energy stimulus, which are tissue-modified energy responses, processing tissue responses, and analyzing processed tissue responses (US Pat. No. 5,042,494).

 The same patent discloses a device for diagnosing a precancerous or cancerous state of tissue, containing a single probe for exposing the tissue to energy stimuli, sensitive elements, each of which is capable of perceiving the tissue response to the corresponding energy stimulus, which is a response energy signal, a controller connected with sensing elements for obtaining said tissue responses, and comprising a processor for processing said tissue responses and copost Avleniya obtained results, and a memory block.

 Further, from US Pat. No. 5,042,494, there is known a method for diagnosing a precancerous or cancerous state of a tissue, comprising exposing the tissue to an irritant in the form of electromagnetic radiation of several wavelengths, followed by processing the tissue responses to electromagnetic radiation, which are the radiation scattered by the tissue, and analyzing the processed tissue responses .

 Finally, from this patent there is known a device for diagnosing a precancerous or cancerous state of tissue, comprising an electromagnetic radiation source configured to irradiate tissue with electromagnetic radiation of at least two different wavelengths, connected to it a single probe for transmitting electromagnetic radiation to the tissue and receiving scattered by it radiation at the corresponding at least two different wavelengths, a receiving device connected to the probe, and a comparison device for comparing the responses t cans for electromagnetic radiation, which are the response radiation scattered by the tissue, with known values.

 The above methods and devices have several disadvantages. In particular, each of these methods and devices is intended for diagnosis in relation to a specific type of cancer, which is presented to a doctor in idealized conditions. Therefore, such methods and devices cannot be effectively used for a large number of varieties of tissues and cancer, such as cancer of the cervix, skin, colon, etc., and are inconvenient for the detection of cancer in the places noted above.

 The basis of the present invention is the creation of a method for the diagnosis of precancerous or cancerous state of tissue, which, due to the choice of certain stimuli of tissue allows you to quickly conduct objective recognition of tissue types, including both cancerous and precancerous lesions, in relation to various locations both inside and in other places of living substance, as well as the task of creating a device for implementing the method.

 This problem, according to the first aspect of the invention, is solved by a method for diagnosing a precancerous or cancerous state of tissue, including exposure to tissue with energy stimuli, determining tissue responses to each energy stimulus, which are tissue-modified response energy signals, processing tissue responses, and analyzing processed tissue responses in which, according to the invention, the tissue is exposed to at least two stimuli, the processing of tissue responses is carried out vlyayut by their combined treatment for tissue classification and an analysis of the treated fabrics made by comparing the responses obtained with the known classification of the tissue classifier of expected tissue types to its recognition.

 Preferably, the stimuli are selected from the group consisting of electric energy sources, light energy sources, acoustic energy sources, magnetic energy sources and thermal energy sources.

 It is advisable that at least one of the stimuli is selected from the group consisting of energy sources generating a continuous annoying signal, a pulse-modulated annoying signal, a frequency-modulated annoying signal, a phase-modulated annoying signal, and an amplitude-modulated annoying signal.

 It is desirable that one or each selected stimulus be a light energy source generating a sequence of a plurality of pulsed light signals, each of which has its own spectral frequency band, the sequence being repeated with the possibility of substantially simultaneously obtaining the corresponding tissue responses.

 It is possible that the processing of each response was carried out by means of one or several predetermined processing steps to obtain a processing result at one or each step, and if there are several processing steps, each processing result was combined in a predetermined manner to classify the fabric.

 It is useful that the number of processing steps be greater than the number of irritants used by an amount equal to 1.

 It is preferable that sources of electric energy and light energy sources are used as stimuli, allowing eight processing results to be obtained.

 It is advisable that the processing results are combined by means of their weighted summation with a given weight coefficient for each processing result, based on the types of fabric in the classifier and on the correspondence of each processing result to the classifier.

 It is desirable that the processing results be combined using linear programming, cross-correlation, or neural networks.

 It is possible that the classifier of expected tissue types was created by cross-matching manually examined and pathologically classified samples of recognizable tissue types with processed tissue sample responses obtained by exposure of the tissue to stimuli and combined processing of tissue responses to each stimulus.

 It is useful that one or more kinds of tissue of the cervix, breast, skin, prostate or colon be examined.

 Preferably, the combined processing and comparison of the classified tissue with the classifier is performed in real time, and statistical methods are used to compare the classified fabric with the classifier.

 It is advisable to examine tissue that is part of a living organism.

 It is desirable that at least sources of electrical energy and sources of magnetic energy be used as stimuli, and the combined processing of tissue responses is carried out by processing the amplitude response, frequency response, absolute amplitude determination, phase response, spectral response, response with respect to the coefficient of the first derivative with respect to time, or response by the coefficient of the second time derivative.

 It is possible that at least light energy sources were used as stimuli, and the combined processing of tissue responses was performed by processing the amplitude response, spectral response or spatial response.

 It is useful that at least sources of acoustic energy are used as stimuli, and the combined processing of tissue responses is carried out by processing the amplitude response, phase response, or frequency response.

 This problem, according to the next aspect of the invention, is solved by means of a device for diagnosing a precancerous or cancerous state of the tissue, containing a single probe for exposing the tissue to energetic stimuli, sensitive elements, each of which is capable of perceiving the tissue response to the corresponding energetic stimulus, which is a response energetic a signal, a controller connected to the sensing elements to obtain the indicated tissue responses, and containing the process quarrels for processing these tissue responses and comparing the results obtained, and a memory unit, in which, according to the invention, a single probe for influencing tissue contains many energy sources, and the memory unit is configured to store a known classifier of expected types of tissue, the processor is configured to combine processing tissue responses to each stimulus to classify the tissue and with the possibility of comparing the resulting tissue classification with a known classifier of expected tissue types for I recognize her.

 Preferably, the controller comprises an indicator for indicating to the user the type of tissue being recognized.

 It is advisable that the single probe is an operator-controlled probe for contacting the tissue, with energy sources and sensing elements embedded in the probe for examining the tissue inside or on the outer surface of a living organism.

 It is desirable that the controller includes means for identifying the probe’s summation of the irritation to the tissue to digitally record each use of the probe and to automatically limit the number of reuse times.

 This problem, according to another aspect of the invention, is solved by means of a device for diagnosing a precancerous or cancerous state of tissue, comprising an electromagnetic radiation source configured to irradiate tissue with electromagnetic radiation of at least two different wavelengths, connected to it a single probe for transmitting electromagnetic radiation to the tissue and receiving scattered radiation at the corresponding at least two different wavelengths, a receiving device connected to the probe and a comparison device for comparing tissue responses to electromagnetic radiation, which is a tissue scattered response radiation with known values, in which, according to the invention, the probe comprises at least one electrode for applying electrical signals to the tissue and its corresponding electrical measuring means for measuring the resulting response tissue to electrical signals, and the comparison device is configured to compare tissue responses to electromagnetic radiation of the tissue and the result the response of tissue to electrical signals with corresponding known values to identify the type of tissue.

 This problem, according to the last aspect of the invention, is solved by a method for diagnosing a precancerous or cancerous state of the tissue, including exposure of the stimulus to the tissue in the form of electromagnetic radiation of several wavelengths, followed by processing of tissue responses to electromagnetic radiation, which is a response radiation scattered by the tissue, and analysis processed tissue responses, in which, according to the invention, electromagnetic irradiation of the tissue is carried out at least two different lengths waves supplied to the electrical signals from the tissue by measuring the resulting response of the tissue to electrical signals, in combination treated tissue responses to electromagnetic radiation and the resulting tissue response to electrical signals, and diagnostic analysis is performed by comparing tissue treated tissue responses with a predetermined expected tissue response.

 It is preferable that, based on the combined processing of the tissue responses, it is classified and the classification of the tissue is compared with the existing classifier of expected types of tissue for its identification.

 It should be noted that in cases where the term "wavelength" is used in connection with a source of electromagnetic radiation, the bandwidth of such a source should be limited.

 It should also be noted that backscattering radiation includes radiation due to reflection.

Embodiments of the present invention will be described with reference to the following drawings:
FIG. 1 illustrates a section through one embodiment of a probe;
FIG. 2 is a schematic illustration of a first embodiment of a probe;
FIG. 3 is a schematic illustration of a second embodiment of a probe;
FIG. 4 is a graph of a sequence of electrical pulses used in the embodiment of FIG. 2;
FIG. 5 is a sequence chart of electrical pulses used in the embodiment of FIG. 3;
FIG. 6 is a block diagram of a detection system of one embodiment of the invention;
FIG. 7 is an example of a graphical representation showing a group of tissue types as a function of three discriminants obtained from electrical and optical measurements;
FIG. 8 illustrates the use of an embodiment of a probe for detecting a precancerous condition of the cervix;
FIG. 9 illustrates another embodiment of a probe for detecting skin cancer or the like;
FIG. 10 is a partially cutaway isometric view of another embodiment of the invention for detecting skin cancer or the like;
FIG. 11 is a side view of an optical sensor, including a spherical refractive head;
FIG. 12 is a view of another embodiment that includes ultrasonic transducers;
FIG. 13A and 13B are rear and side views of an embodiment of a probe that includes thermal and optical stimulants;
FIG. 14A and 14B are rear and side views of an embodiment of a probe that includes electrical, optical, and magnetic stimulants;
FIG. 15 and 16 illustrate two devices for calibrating the probe;
FIG. 17 illustrates a further embodiment of a device for calibrating a probe;
FIG. 18 is a block diagram of a preferred embodiment of an apparatus for detection.

 Detection of cancer using optical sensing is to display the studied tissue site on the sensor array. This method has a number of limitations.

 First, when cancer is detected, transmission through the tissue and scattering by the tissue and its adjacent areas is more important than reflection from the surface of the tissue. Optical image sensors initially respond to reflection from the surface of the fabric.

 Secondly, the identifiable image depends on the mutual influence of a number of characteristics of the state of the tissue, such as reflectivity, emissivity, specular reflection, liquid on the surface and ambient lighting.

 Thirdly, the optical signal received by each image element of the sensor matrix is decomposed in the camera into only a few spectral regions corresponding to red, green, and blue (R G B) radiation.

 Fourth, it is not physically feasible to simultaneously make electrical, magnetic, or acoustic measurements for each projected tissue element. It is believed that such measurements in combination with optical information can be very important for distinguishing between tissues in the indicated area.

 In addition to the foregoing, we note that the study area is not always sufficiently accessible for lighting and recognition using devices such as a camera.

 When a tissue is examined with the naked eye or with an imaging system, the pattern we observe is the light reflected by every tiny patch of tissue. This light is the result of reflection from the surface, and it can be affected and even suppressed by liquids, oxidizing substances and other chemicals or phenomena that exist on the surface, depending on the pH of the surface, temperature, and also on the type and angle of illumination. Light reflected from cells and tissues located on or near areas of the surface carries less information related to a precancerous or cancerous condition compared to cells or tissues lying deeper, the visibility of which is significantly weakened due to surface reflection .

 Therefore, devices that allow penetration, for example, by means of a signal to the optical properties of deeply located cells, are excluded, while excluding reflections from cells located on the surface.

 The means used in the described construction to achieve such recognition are based on controlled spatial separation and optical isolation between the tissue regions where it is irradiated and the tissue region whose radiation is analyzed.

 Inspection with the naked eye or using a conventional optical detection system is not equivalent to the means described above when studying the transfer properties of each element of a tissue site.

 These properties are the result of the complex dynamics of the processes of transmission, absorption, scattering and back reflection, the final result of which can make the identification of tissue more reliable compared to using only surface reflection.

 This complex process, represented by the term "backscatter," underlies the basic embodiment of the device described below.

 When information from a plurality of nearby areas, the backscattering characteristic of which is measured, is restored in the form of an optical image (that is, it is restored in the same spatial order in which the measurements were made), an “image” of back-scattered values of the reconstructed surface is formed.

 Such an image, called a "backscatter image", can provide a valuable image that allows you to distinguish between the types of cells and tissues of the entire area.

 In one embodiment of the present invention, means are provided for creating such backscattered images.

 Complementing the above with electrical measurements reflecting the dielectric properties and impedance of the tissue of each image element, allows you to create a multidimensional picture of the image.

 The described backscattering image acquisition mechanism is based on the concept of measuring any one or more electrical, magnetic acoustic, ultrasonic, thermal, optical, and other similar physical parameters of each image element related to the described images.

 Thus, each element of the scattered image may contain characteristics of various types of energy and physical mechanisms.

 Although changes in the backscatter signal mainly reflect the excitation / reception transfer characteristics, one should not exclude measurements of the intrinsic characteristics of each image element (such as the prevailing temperature, electrostatic potential) when determining the backscatter image.

 Since in determining cancer it is extremely important to asymptotically strive to obtain a false false result, it is highly advisable to use the maximum possible number of independent discriminators to recognize tumor cells.

 For example, if, when recognizing types of tumor cells, the statistical contribution of this device for excitation / reception, which includes an independent type of energy, is 1%, and the total effect introduced into the statistical recognition of other types of energy, for example optical or electrical), is 98%, then a 1% contribution made due to magnetic energy will halve the system error from (100% - 98%) = 2% to (100% -99%) = 1% (for optical, electrical and magnetic energy). Thus, the contribution of an independent, insignificant in terms of magnitude statistical recognition ability allows a significant increase in the performance of the entire system, which indicates the introduction of independent types of energy.

 For this reason, multiple measurements that are applied to many forms of energy and mechanisms (albeit more cumbersome to perform or difficult to integrate into a small probe due to the difficulties associated with microminiaturization) are highly desirable for the preferred design.

 Therefore, you should use a probe configuration that allows easy access to the desired tissue surface, as well as circumventing some or all of the limitations mentioned above.

 If cancer is detected in the vicinity of the area penetrated by a physical probe, it is important to have access to the surface of the tissue being examined that allows visual feedback to increase the efficiency of the doctor.

 Therefore, constructions where a sensor is used must be shaped so as to provide maximum visibility with minimal dimming, allowing stimulating sensors to follow the outlines of the tissue being examined. The accuracy with which the type of fabric can be determined near the surface is largely dependent on the above operations.

 Control of orientation with respect to the surface of the fabric, pressure on the surface of the fabric, elimination of undesirable sources of instrumental noise, such as light background, liquids, spurious electromagnetic or mechanical vibrations, are important factors that influence the achievement of accurate measurements.

 In addition, these factors limiting the accuracy of measurements are interrelated and depend on the methods of transfer of stimulating energy to and from the surface of the tissue, regardless of whether the stimulus energy is electric, optical, acoustic, magnetic, thermal or ultrasonic.

 Using the image sensor, one should accumulate the data set of each area of the interrogated space, so that the decision about the area was based not on one, but on the set of N samples.

Также целесообразно иметь возможность установить сходство между результирующей "картиной" каждой клетки или каждого вида ткани изучаемой области и картинами на экране компьютера, извлекаемыми из системы формирования изображения. Для этого при построении устройств обнаружения предракового и ракового состояния, которые измеряют физические изменения, следует предусмотреть систему сбора данных, способную адаптироваться ко множеству типов зондов, каждый из которых имеет специфическую конструкцию, определяемую характером его применения. Поэтому зонды должны быть взаимозаменяемыми и автоматически калиброваться при замене.The result of such processing of samples is equivalent to an increase in accuracy proportionally

It is also advisable to be able to establish similarities between the resulting "picture" of each cell or each type of tissue in the study area and the pictures on a computer screen that are extracted from the image forming system. For this, when constructing devices for detecting precancerous and cancerous conditions that measure physical changes, a data collection system should be provided that can adapt to many types of probes, each of which has a specific design, determined by the nature of its application. Therefore, the probes must be interchangeable and automatically calibrated when replaced.

 It is also important to provide the doctor conducting the test with feedback for cases of improper use of the probe, disorientation, inconsistencies, or other conditions that may lead to erroneous results during the test.

 Such information should come immediately or be readily available along with other warning alarms associated with the instant approach of the probe to precancerous or cancerous tissue.

 During the tests, the doctor’s actions are most likely focused on manipulating the probe in the area of the tissue being studied, and therefore he cannot focus on the computer screen or other display devices.

 Systems that provide the doctor with adequate real-time feedback and at the same time allow storing the necessary measurement data are important components of a cancer diagnostic instrument.

 Since the sensors usually work in an environment containing liquids, the optical and electrical characteristics of which vary, there are difficulties in calibrating the transmitting and receiving probes, as well as the electric channel, due to the need to monitor these changes.

 It is desirable that the optical measurements are based on the characteristics of the transmission, absorption and backscattering of the body, and not on the reflectivity of its surface.

 Setting the probe tip normally to the reflection standard for calibration gives a response mainly due to surface reflection of the standard. With such a calibration, the radiation / reception ratio will not be a monotonic function of the distance between the reflection standard and the active part of the probe and will depend strongly on the distance.

 Thus, the difficult task reproduces the actual conditions of real measurements carried out during the calibration process.

 In a probe that is controlled by an operator and periodically contacts the surface of the fabric, the temperature of the semiconductors and other elements will vary due to the difference between the temperature of the fabric and the environment. In particular, for elements that contain semiconductor junctions on the active surface of the probe, temperature changes can lead to significant changes in operation. Therefore, it is desirable that during the measurement, the data processing system compensates for these temperature changes.

 Currently, the main mechanisms that cause physically measurable differences between normal, precancerous and cancerous tissue types are presented only from the point of view of the phenomenological model.

 For an arbitrary type of cancer, no one can predict the exact value of each distinguished parameter. As a result, the calibration process for a cancer detection device is directly related to the discrimination algorithm used and the basic measurements that this algorithm relies on. This means that the operation algorithm can only be correctly optimized when reliable data on the cancer and precancerous condition are collected using a stable reproducible probe with the required geometry and electro-optical characteristics (for example). Therefore, methods for optimizing the algorithm using successful iterations become part of the calibration process, and the necessary tools for this are implemented using various devices.

 To obtain discriminants of different types of tissue, one or more electrodes can be used. When one electrode is used, the patient is grounded by contact with another part of the body. For example, in cardiology, when using one electrode for reading data, one arm is in saline solution, or a cuff is attached to her wrist.

 The use of a set of electrodes makes it possible to use their relative readings to confirm that other measurements, for example, optical, were carried out correctly using optical transducers that are correctly installed in relation to the surface of the fabric. Asymmetric readings from asymmetrically located electrodes indicate an asymmetry of the probe tip with respect to the tissue surface.

 The electrodes can be made in the form of metal disks on the front of the insulator, which is achieved by using a wire with a truncated surface.

 The electrodes can be of any shape, in particular round, elliptical, square, rectangular, triangular, circle segments or ring segments, and their orientation can be symmetric or asymmetric with respect to the center of mass of the tissue region under study.

 The surface of the electrode, in turn, may be metallic or non-metallic. In particular, the electrode may include a semiconductor material, for example, silicone, graphite or titanium dioxide supported on titanium.

 In another embodiment, the electrode may include an electrolytic cell (e.g., silver / silver chloride, or mercury / mercury chloride) bonded to the fabric via a salt bridge.

 The salt bridge is an electrolyte containing a gel, spongy or porous connector, and can also be used in conjunction with a metal electrode.

Electrodes can be used to measure a number of electrical characteristics such as:
- Conductivity, by determining the current flowing when a sinusoidal voltage is applied to the electrodes (in the frequency range);
- The complex resistance of the system in the frequency range;
- The current flowing into the electrodes attached to the tissue when voltage is applied to them. This current can be analyzed by time or frequency methods (for example, the Fourier transform).

 Temporal analysis can be presented in the form of a curve of the current shape versus time, parameters in the equation of the curve, or the values of the components of the equivalent electrical circuit.

 - The current flowing from the electrodes of the tissue after the termination of the voltage pulse applied to the electrodes. Here, as in the examples described above, the analysis can be performed in both the time and frequency domains.

 - The voltage drop without current flow after removing the applied voltage, which was kept constant until it was removed, enough time to reach the steady state (i.e. voltage drop at a very high resistance).

 The electronic device used to perform the above measurements may be hardware or a computer running software. In the latter case, the type of measurements performed may vary depending on the results of previous measurements. These tools are important for ascertaining that the probe is mounted accurately on the surface of the fabric, and therefore the readings, as well as the electrical, optical and other paths, can be considered reliable.

 Data can be deleted automatically if the orientation of the probe is out of range.

 For compatibility with software, various electrode and circuit configurations can be selected for signal analysis.

 For some types of tissue, the computer may not be able to give an unambiguous diagnosis using the standard measurement mode. In this case, the circuit can be changed programmatically or by other means by which additional definitions can be made.

 The probe should be able to quickly move around the surface or inside the human body using an expander or other auxiliary devices that provide the doctor with an unobstructed view of the probe tissue. In addition, sufficient clearance must be provided for the penetration of bright light, for example, when conducting video recording of sample data.

 For most intracavitary applications, the size of the surface to which the probe is applied to provide a response may be less than 2 mm in diameter. Accordingly, the resolution of the probe should be sufficient to resolve precancerous tissue of this size.

 Having established a number of preferred criteria that may be useful for determining precancerous and cancerous tissues, we proceed to describe specific structures.

 In FIG. 1 shows a device for diagnosing precancerous and cancerous tissue, including a probe 1 connected to a controller 20 via a cable 9 connected to a probe 1 through a connector 8. In this device, a probe 1 is used to detect cervical cancer. In FIG. 1 also shows an expander 30, which is used to open the walls of the vagina 31 of the patient for exposure to the probe tip 1; the cervix 32 completes the birth canal 33 leading to the uterus 34.

 The probe 1 moves along the entire surface of the cervix 32 in order to stimulate the tissue of the uterus 32 and receive responses to stimuli that can be processed by the controller 20.

 As shown in FIG. 2, the probe 1 includes an outer tube 2, which provides electrical insulation and creates mechanical strength. Located inside the tube 2, the first electrode 3 is made in the form of an electric wire with a truncated surface and is located in the center of the bundle of fiber optics 4.

 The other three electrodes 5, 6, 7 are segments of a cylindrical metal tube that are adjacent and abut against the inner surface of the outer tube 2. FIG. 3 shows a second embodiment of the probe 10, which is used in the device of FIG. 1. This version of the probe 10 has a more compact design, which is implemented using only three electrodes 15, 16, 17, having a shape different from the electrodes 5, 6, 7.

 The shape of the electrodes 15, 16, 17 provides electrical and optical measurements on the same tissue site.

 The electrodes 15, 16, 17 are adjacent and abut against the outer tube 12 together with a cable of three fiber-optic bundles 14 located between them.

 Using the first version of the probe 1, three initial electrical measurements are made between the central first electrode 3 and each of the remaining electrodes 5, 6, 7. The results of these measurements are compared, and if they differ significantly, the measurements are discarded, because they indicate uneven contact of the probe tip 1 with the tissue.

 In a preferred embodiment, pulse methods are used to measure electrical and optical properties, as they reduce noise and the mutual influence between the measured signals. Therefore, in the examples of the invention shown in FIG. 4 and 5, a sequence of electrical pulses is used.

In FIG. 4 shows the sequence
electrical pulses, which can be used for the probes of FIG. 1 and FIG. 2.

 A voltage pulse of U3.5 is applied between the electrodes 3 and 5, while the electrodes 6 and 7 are disconnected.

 This pulse is followed by a pulse U3,6 between electrodes 3 and 6 when the electrodes 5 and 7 are switched off. Next is the pulse U3,7 between electrodes 3 and 7 when the electrodes 5 and 6 are turned off. During and immediately after each pulse U3,5, U3.6 and U3.7 measure electrical responses, which are then stored and compared. This is described below. If the measurement results differ significantly, they are discarded, because this indicates that the tip of the probe 1 has uneven contact with the tissue.

 To be able to obtain a large number of samples, the pulse duration and the duration of the sequence should be relatively short: typical values of the pulse duration from tens to hundreds of microseconds with a sequence duration of a few milliseconds will provide useful information in real time.

 If the above measurements show that the probe 1 is installed correctly, the fourth measurement is performed with a symmetrical connection of the electrodes, i.e., a voltage pulse U3 (5, 6, 7) is applied between the electrode 3 and the electrodes 5, 6, 7.

 In FIG. 5 shows a similar sequence of electrical pulses used for the embodiment of FIG. 3. In this embodiment, the electric field will not be balanced at the moment.

 Three electrical pulses are applied between the electrodes: U15 (16.17) is applied between the electrode 15 and the connected electrodes 16 and 17, U16 (17.15) is applied between the electrode 16 and the connected electrodes 17 and 15 and U17 (15.16) is applied between the electrode 17 and the connected electrodes 15 and 16. The relative values of the measured responses indicate the correctness or incorrectness of the installation of the probe, which provides an indication of operator error.

 In another embodiment of the invention, only one electrode is allowed to be used in the probe, the second connection to the skin or tissue can be accomplished in one of many acceptable ways, for example, using a conductive cuff connected to any part of the body.

 Using probe 1 or 10 of the described embodiment of the invention, it is possible to determine the electrical properties of the fabric in many ways. For example, a rectangular electric pulse can be applied to the electrodes as described above, and the time-varying current that flows in and out of the tissue can be measured either in the form of a current in the circuit or in the form of a time-varying potential difference between the electrodes, following the impulse.

 The shape of these time-varying signals is a measure of the electrical characteristics of the tissue. Alternatively, electrical signals of different frequencies can be used to measure the electrical characteristics of the tissue. The voltage level applied to the tissue during the measurements should be large enough so that the measured signals exceed the surrounding noise signals (which may be present), but in general they should not exceed 2 V so as not to cause discomfort for the patient.

 The optical characteristics of the tissue can be measured in the wavelength range from ultraviolet to infrared.

 One of the optical fibers in probes 1 and 10 is used to direct electromagnetic radiation from one or more sources to the surface of the tissue, where energy is absorbed and scattered. A second fiber, which may be adjacent or adjacent to the first fiber, directs radiation from the tissue to one or a number of detectors (not shown). The amplitude of the signals from the detectors is a measure of the optical characteristics of the tissue.

 Light emitting diodes (not shown) or solid-state lasers (not shown) can serve as sources of electromagnetic radiation.

 Several wavelengths can be directed along a single 4.14 fiber, or individual 4.14 fibers can be used for each wavelength. Among the wavelengths that are considered the most acceptable for diagnosis are 540, 650, 660, 940 and 1300 nm.

 The controller 20 includes a specialized computer system 21 (Fig. 6) and can control devices of the preferred design.

 The system 21 includes a microprocessor unit 22, which controls, through an analog unit 23, the synchronization of electrical signals applied to the electrodes 3, 5, 6, 7, 15, 16, 17 of the probes 1 and 10, respectively, and to optical emitters (not shown). The signals from electrical and optical detectors are processed in the microprocessor unit 22, and the processing result can be displayed on the display 24 or can activate the operation of other indicators: visual, audio, printing device. To enter commands into the computer system 21, the operator can use the keyboard 25.

 The data collected by the computer system 21 are processed and compared with the data that were stored in its memory in the form of image data specific to each type of tissue.

 In FIG. Figure 7 shows a typical graph of tissue appearance obtained as a result of electrical and optical measurements as a function of three discriminants.

 When constructing FIG. Three discriminants are used in Fig. 7: two — the result of measuring the backscattering of light (dsc1, dsc2 — each at the corresponding wavelength), and one — the result of measuring the shape of the electric relaxation curve obtained using Fourier analysis (dsc3).

 FIG. 7 shows the difference between normal types of tissue - congenital squamous epithelium (OSE1, OSE2, OSE3), cylindrical (COL1, COL2) and immature metaplasia (P) from pathological - precancerous tissue such as Human Wart Virus (HPV), Atypia (ATVP) and precancerous ( D1, D2, D3).

 The results of these comparisons are communicated to the operator using the display 24 or other suitable means. For each patient, these results can be stored in microprocessor unit 22 and then selected from memory or printed out.

 As shown in FIG. 1-7 embodiments, probes 1 and 10, having, in certain cases, an elongated outer tube, can be made with a flexible handle or the probe can be integrated into the capsule by insertion into it by the principle of a catheter.

 In FIG. 8 shows a probe 40 designed to solve a specific problem, having the shape necessary for examining tissue samples of the cervix 32 of a patient. In particular, the cervical probe 40 has an elongated handle 41, for which the doctor can hold the probe and which is connected by a cable (not shown) to the control system. The handle 41 is bounded by the main body 42, from which the central portion 43 of the probe branches into the birth canal 33 and is surrounded by an annular recess 44 having the shape of a cervical cup.

 Along the surface of the probe 43 and the recess 44 there are repeated rows of stimulation / receiving elements 45 that have been given the necessary shape to test the physical characteristics of the tissue along the inner outline of the cervix 32.

 Sensors 45 are connected to the controller via a knob 41.

 Since the variety of types of stimulation / reception energy is applied to the set of adjacent regions along all the outlines of the front of the probe, the combined backscatter pattern can be obtained by simply turning the handle 41 by the operator.

 In FIG. 9 shows a flexible probe that is designed specifically for the skin, in this case, for the skin of the arm of a patient 36. The probe 50 consists of a flexible flat printed circuit board 51 on which a number of sensors are located. Sensors 52 are connected to cable 54 via printed connections 53. Cable 54 connects probe 50, as in the previous embodiment, to the controller. Due to this construction, the probe 50 can be applied to both a curved and a flat surface, which makes it possible to evaluate relatively large areas in a significantly shorter time than that required by the probes of the embodiments of FIG. 2, 3 or 8.

 In FIG. 10 shows a further development of the structure of FIG. 9, but for a fully integrated detector assembly. The detector assembly 60 includes a flexible substrate 61, on which, like the probe 50, a plurality of sensors 62 are mounted. The substrate 61 is held by a support 63 made of open cell foam and attached to the casing 64, within which the device is located the control 65 of the detector assembly 60. The support 63 allows the substrate 61 to bend to fit the outlines of the fabric, while being supported by the control device 65. The control device 65 is connected to the sensors 62 and introduces into the small-sized unit and data processing required to determine the appearance of the outer tissue.

 The control device 65 includes a power supply 66, consisting of a set of batteries, and a processor module 67, the input / output section 68 of which is connected to the sensors 62 and the control / display module 69. The indicators 70 connected to the control / display module 69 provide a visual or audible feedback from the operator and indicate the type of tissue when the combination of sensors 60 is installed on the surface of living tissue.

 FIG. 11 illustrates a spherical refractive probe 71, which includes a pen body 72 and a clean (transparent) spherical refractive ball 73 mounted on the periphery of the pen body 72. Light sources 74 are integrated inside the pen body 72 (only one of them is shown in FIG. 11) , such as LEDs emitting in different spectral regions, and sensors supplementing them 75 (only one of them is shown in FIG. 11 for clarity), such as light-dependent resistance, PIN diodes, or other optical sensors. The probe 71 is designed in such a way that the ball 73 refracts the light rays emitted by each source 74, forming a generally spherical waveform to act on large portions of the surface of the fabric 76 that are in contact with the ball 73. Similarly, the light backscattered from the fabric 76 is refracted through the ball 73 towards the sensor 75. The optically opaque barrier 80a prevents direct illumination on the way from the source 78 to the sensors 79. In order to provide contact with the tissue 76 for its electrical stimulation, on the ball 73 r found on the rear electrode 78. The two signals between the probe 75 and controller (not shown) are passed through a series of wire leads 80. As seen from FIG. 11, the region 80 of the fabric 76 is illuminated by sources 74, and the area 81 of the fabric is inspected by sensors 75, which provide an indication of light transmission through the fabric 76 between areas 80 and 81.

 In FIG. 12 shows an ultrasonic transducer 85, which is mounted on the upper part of the handle 86, into which four electric transducers 87 are designed, designed differently from the previous design. In particular, four ultrasonic emitters 88 are installed in the probe 85, each of which can be independently excited in order to stimulate tissue in contact with it. When any of the emitters 88 stimulates the tissue, the other three can be used to receive the transmitted ultrasound radiation. Received ultrasound signals can be processed to determine differences in characteristics associated with tissue density and any changes in density in any part of the tissue where blood flow is indicated. This can be done by measuring the travel time, in the same way as in known acoustic imaging systems, such as sonar or ultrasonic medical devices. In order to compensate for changes in acoustic coupling, a number of temperature sensors 89 are installed on the surface of the probe 85, which can be used to determine the temperature of the tissue under study in order to compensate for changes in the speed of ultrasound.

 In FIG. 13A and 13B depict a probe 90 using heat and light energy, which consists of a body 91 made in the form of a pipe along which optical fibers 92 extend.

 Optical fibers 92 are used to illuminate the test tissue and receive light reflected from the tissue. A heating element 93, designed to selectively heat the probe tissue, and a temperature sensor 94, designed to measure the temperature of the tissue as a response to the action of the heating element 93, are also introduced into the probe 90. The response time of the tissue type to the thermal effect can be determined using a controller that provides indications of blood flow in the tissue, which can serve as an indication of precancerous and cancerous formations.

 In FIG. 14A and 14B depict a magnetic probe 100, which, similarly to the previous embodiment, is provided inside the tube-shaped housing 101. The probe 100 includes a series of electrodes 102 designed in a manner similar to the previous embodiment. Four optical transmitters 103 were also introduced there, such as LEDs, designed to transmit light at different wavelengths such as 1300, 440, 565 and 660 nm. To receive light of various wavelengths, such as 1300 and 500-1000 nm, two optical detectors 104 are installed. In addition, a magnetic radiation transmitter 105 mounted in the center of the probe 100 and three surrounding magnetic radiation receivers 106 are introduced.

 The transmitter 105 and the receiver 106 of magnetic radiation contain a magnetic core with a winding, while the transmitter of magnetic radiation 105 creates a small magnetic field extending from the end of the probe 100. Changes in the magnetic field are detected by receivers 106, which can compare by imbalance between the signals received by each of the receivers 106, which allows you to determine the magnetic anomaly in the tissue.

 Although at the time these materials were being written, the exact meaning of magnetic stimuli was not clarified, it is believed that localized anomalies in the magnetic response of the tissue are caused by imbalances in the electric charge resulting from changes in the separating layers inside the tissue cells. Note that the environment of the tissue nucleus is a series of shells separated from each other, and it is believed that the connection between them limits the growth of normal cells. However, in the case of cancer cells, the limitation of the connection between the membranes seems to be precisely the limitation that is directly related to the unhindered growth of cancer cells. Therefore, an imbalance in the distribution of the electric charge, which can be determined or changed using a magnetic field, can serve as an indicator of a limited connection and, therefore, a cancerous state. For different types of probes, it is desirable to use a common control device, and therefore it is appropriate that, where the probes are interchanged, they and / or the controller can be calibrated in such a way as to ensure reliable and consistent examination of the samples.

 The rapid growth of microminiaturization increases the possibility of realizing in a single probe a significant number of the previously mentioned forms of stimulation / reception energy, which increases the number of distinguishable parameters required for determining cancer and precancer.

 In FIG. 15 depicts a first calibration design 120, where a probe 122 connected to a controller 121 is in contact with an artificial tissue substitute 123. Material 123 mimics well-known known tissue characteristics, such as backscattering and other energy characteristics associated with radiation / reception, such as electrical, while the controller 121 can be set to automatic zeroing, in which the output of stimulating pulses from the probe 122 and the received signal can be within normal limits or adjusted so that They returned within established boundaries. Once calibrated, the probe 122 can be used for work, and the artificial tissue substitute 123 must be sterilized to prevent biohazard.

 In FIG. 16 shows a second structure 125, which is fully active as opposed to the semi-active structure of FIG. 15. In FIG. 16 shows the tip of the probe 126 in contact with the matrix 127 that complements it, which forms part of the controller 128 that communicates with the probe 126. Thus, the transmitters and receivers of each of the tips of the probe 126 and the matrix 127 can be excited, and since the output signal of the matrix 127 the probe is known and consistent with the precisely calibrated configuration of the driver 129, the output of the driver 129 can be determined by a calibrator controller 130, which can modify the configuration of the probe tip driver 126. The third calibration device 135 redstavleno FIG. 17, where the probe 136 has conductive wires 137 coming from a sensor (not shown) and connected to the controller 141. The probe 136 has a programmable read-only memory device (PROM) 138, which contains data on special calibration values associated with the sensors the probe 136. The EPROM 138 is directly connected to the calibration module 140 via wires 139. The calibration module 140 has outputs 142 for adjusting the gain associated with an array of amplifiers 143, to which wires 137 are connected to and from the sensors. Thus, the gain of each amplifier 143 is adjusted in accordance with the data provided in the EEPROM 138 to compensate for the differences between the sensors of different probes 136. The EPROM circuits 138 also allow digital electronic standardization of the probe and allow tracking when the probe is used with a computer. The introduction of the PROM 138 into the probe 136 allows electronic recognition of the probes, with each use of the probe 136 is fixed; if necessary, the number of re-use of the probe 136 is limited a priori automatically.

 We now turn to FIG. 18, which schematically shows a preferred design of the detection system 150, which includes a probe 151 connected through an analog board 152 to a processor board 153. The processor board 153 on the output side is connected to the display 154 and has user inputs that are connected via control keys 155 and a specialized digital keyboard 156. The computer mode of communication is through the RS-232 connection (interface for slow devices) 157 or the IEEE 488 port (interface for devices with an average data rate x), or COM # port, or direct memory access (DMA); The mains voltage is supplied through connector 158.

 Probe 151 contains devices that create many different physical stimuli. In particular, LEDs 159 provide optical stimulation. The electrodes 160 provide electrical stimulation of the tissue, which can be used both to determine the value of the discriminant, and to assess the position of the probe 151 relative to the tissue. Additional devices (not shown) to increase the number of discriminant stimulation / reception can be introduced by analogy with those described. To increase the orientation of the probe 151, strain gauges 161 are used, which provide an indication of the position of the probe 151 relative to the fabric. The sensor 161 also contains indicators 162, which can be audio and / or optical, and provide real-time feedback between the physician and the type of tissue being examined. Photodiodes 163 provide electro-optical perception of the light emitted from the LEDs 159 and reflected from the tissue. Due to the low level of the output signal of the photodiodes 163, preamplifiers 164 are introduced into the probe 151. The probe 151 is connected to an analog board 152, which contains a power amplifier and a control amplifier associated with each of the elements of the probe 151. The processor board 153 includes a controller using a central a processing unit (CPU) 178, which is equipped with a digital input / output unit (1/0) 176 and a serial input / output unit (1/0) 178. The central processing unit initiates stimuli that are output through the serial unit in od / O 178 to the DAC 174. The output of the digital to analog converter is supplied to the power amplifier and control the amplifier 165 LEDs. A power amplifier and a control amplifier 165 of the LEDs is used to excite the LEDs 159, while digital signals from the digital input / output unit 176 are supplied to its other input. The output of the digital input / output unit 176 is connected to the excitation unit 166, which is connected to the electrodes 160 and supplies on them stimulating impulses that are supplied to the tissue. The amplifier 167 amplifies the output signals of the electrodes 160, which follow through the protection unit 172 to an analog-to-digital converter 177 for evaluation by a central processing unit (CPU) 178. The output of each of the photodiode amplifiers 164 is connected to an amplifier 171 of the optical detector, the output of which is converted to digital form with using an analog-to-digital converter 177 to access a central processing unit (CPU) 178. Alternatively, stimulation / reception emitters can also be introduced. Strain gauge driver 168 uses a direct current signal from a powerful DC converter 180 and feeds it to strain gauge 161, the output of which is connected to amplifier 169 of the strain gauge. The outputs of the amplifier 169 through the protection unit 172 go to the analog-to-digital Converter 177 to measure the magnitude of the forces with which the probe acts on the tissue. The outputs of the digital input / output unit 176 are connected to an indicator amplifier 170 that drives the indicator. The central processing unit 178 includes a reset device 181, a clock 182, as well as outputs connected to a control socket 183. The previously mentioned probe 151 may be equipped with programmable read-only memory (PROM, not shown) to carry out calibration, simplify standardization, and record probe data. When using programmable read-only memory, the latter can be directly connected to a digital input / output unit 176. During operation of the apparatus, the basic stimulation model is programmed or selected from memory 179 using a central processing unit 178 and is used to excite LEDs 159 and electrodes 160. Data series recorded using the central processing unit 178 and stored in the memory 179, where they are converted into various discriminants. For each related series of images taken, numerous discriminants are then combined in accordance with a specific algorithm to provide a classification of tissue types. This classification is then compared with the classification stored in the non-volatile part of the memory (a storage device that stores information when the power is turned off) 179, where the comparison takes place; classification allows you to determine whether the tissue is normal, precancerous or cancerous and provide the doctor with the necessary indication. In cases where the type of tissue is not determined, the appropriate indication is sent to the doctor, which prompts the doctor to conduct further studies of this part of the tissue. When a series of identifiable data is processed, you should choose those signs that are not associated with changes that occur from patient to patient. This may include processing physical parameters such as electrical and optical characteristics in the time and frequency domains to provide frequency and time portraits of electrical characteristics. Frequency components can be obtained by Fourier transform or measurements at different frequencies. Temporal characteristics determine the amplitude of the response caused by the energy supplied to the tissue. Swinging the excitation frequency creates a spectral response, which allows us to consider a tissue type based on complex resistance, including nine or more separate parameters, each of which has a corresponding spectral characteristic. The electrical temporal response can be obtained by sequentially observing the test response to a known electrical effect such as a step function or impulse.

 As noted above, in optical devices the absolute value of the backscattering of the sample can be determined along with the steepness and rate of change of the response, this allows the first and second derivatives to be used as variables as a function of wavelength or time for spectral or temporal characteristics, respectively.

 Since during ultrasound transmission, the change affects the amplitude and the Doppler effect, various combinations are possible, which can be analyzed using the image analysis technique. For magnetic stimuli, anomalies at certain frequencies can be determined. For each type of tissue, different combinations of stimuli can be used.

 For example, for cervical cancer, the preferred types of stimuli are optical and electrical. For skin tissue - optical, electrical, magnetic, acoustic and thermal. To determine the specific type of tissue under study, the obtained physical data and various discriminants should be combined according to a certain algorithm. This can be done using the discriminant analysis technique, linear programming, cross-correlation, or neural network.

 The variant of discriminant analysis is preferable when the expert opinion or empirically obtained correlation is used in relation to data between which there is a relationship in order to optimize the values of the discriminant values. For each variable, various coefficients are evaluated and how the variables should be changed so that they are displayed in the appropriate type of classification.

где VAR_j - переменная в реальном времени, связанная с положением j в линейном уравнении, A_ij - постоянный коэффициент при переменной i и P_i - относительная вероятность i-й классификации ткани.In a preferred device for detecting cervical cancer, eight discriminants are used based on electrical and optical recognition. These discriminants are backscattering of light by wavelengths of 540, 660, 940, 1300 nm and four forms of the voltage damping curve. To perform tissue classification, an algorithmic method is used, and in determining the cancerous and precancerous state of the cervix, using the above identification discriminants, we have

where VAR _j is the real-time variable associated with the position of j in the linear equation, A _ij is a constant coefficient for the variable i, and P _i is the relative probability of the ith tissue classification.

 In order to ensure the accuracy of the test results, a large database is required by which the known responses of specific types of cancer and precancerous tissue could be linked. For example, when creating a device for determining cervical cancer, studies were conducted on 2,000 people, each of which was analyzed by a colposcopist and, in special cases, a histologist, who provided reference data for the most important classes of tissues. Each of these people was also examined using a probe with a device made in accordance with a preferred embodiment, so that the responses of the preferred embodiment to specific types of fabrics that were manually classified can be compared with a classification that was also performed manually . This creates a database for a specific type of cancer, so when the sensor is used for another patient, the responses of this patient after processing by the discriminant analysis method can be compared with the database, which will allow to identify a specific type of tissue.

 Similar experiments were conducted for cancer of the breast, skin, rectum and prostate, and a database was developed for these cases.

 Each new type of cancer leads to new problems in the development of the database. In particular, in vivo studies can be performed for cervical cancer, biopsy results are needed for breast, rectal and prostate cancer, and therefore the database is being developed based on in vitro data. In the case of skin cancer, the results of both dermatological studies and biopsies can be used. The conclusion about the condition of the samples is given by comparing the results obtained using the probe with the results of in vivo recognition, which give reference characteristics for each type of tissue recognized by the probe. A study of the operational data of a preferred embodiment of the invention showed that a detection system 150 (FIG. 18) for cervical cancer provides 85 to 99% correspondence between colposcopy / histology and diagnosis using a probe depending on the degree of abnormality (well-developed changes in the virus human papillomas, slight atypia or intraepithelial neoplasia of the cervix of the first degree), 90% with a high degree of abnormality (intraepithelial scaly neoplasia of the cervix, 2nd il 3rd degree) to 99% of invasive cancer. Statistical analysis and extrapolation of these results suggest that when using the preferred embodiment of the device with a probe, the ratio of false positive and false negative ratings is about 10%, and therefore, for the cervical cancer, the proposed probe design is a significant advance compared to 50-60% -the exact accuracy inherent in traditional methods based on the Papanicolaou test. Above, only certain embodiments of the invention and their modifications are described, which are obvious to specialists in this field of technology and can be performed in the framework of the present invention.

Claims (23)

 1. A method for diagnosing a precancerous or cancerous state of tissue, including exposure to tissue with energy stimuli, determining tissue responses to each energy stimulus, which are tissue-modified response energy signals, processing tissue responses and analyzing processed tissue responses, characterized in that the tissue is affected by by at least two stimuli, the processing of tissue responses is carried out through their combined processing to classify the tissue, and the analysis of botany tissue responses are carried out by comparing the resulting tissue classification with a known classifier of expected types of tissue for its recognition.  2. The method according to claim 1, characterized in that the stimuli are selected from the group consisting of electric energy sources, light energy sources, acoustic energy sources, magnetic energy sources and thermal energy sources.  3. The method according to claim 2, characterized in that at least one of the stimuli is selected from the group consisting of energy sources generating a continuous annoying signal, a pulse-modulated annoying signal, a frequency-modulated annoying signal, a phase-modulated annoying signal, and amplitude-modulated annoying signal.  4. The method according to claim 3, characterized in that one or each selected stimulus is a light energy source that generates a sequence of many pulsed light signals, each of which has its own spectral frequency band, and the sequence is repeated with the possibility of essentially simultaneously receiving the corresponding responses tissue.  5. The method according to claim 1, characterized in that the processing of each response is carried out by means of one or more predetermined processing steps to obtain a processing result at one or each step, and if there are several steps, the processing of each processing result is combined in a predetermined manner to classify the fabric.  6. The method according to claim 5, characterized in that the number of processing steps is greater than the number of irritants used by an amount equal to 1.  7. The method according to claim 6, characterized in that the sources of electrical energy and the source of light energy are used as stimuli, allowing eight processing results to be obtained.  8. The method according to claim 5, characterized in that the processing results are combined by means of a weighted summation with a given weight coefficient for each processing result based on the types of fabric in the classifier and on the correspondence of each processing result to the classifier.  9. The method according to claim 5, characterized in that the processing results are combined using linear programming, cross-correlation or neural networks.  10. The method according to claim 1, characterized in that the classifier of expected tissue types is created by cross-matching manually examined and classified by pathological samples of recognized tissue types with processed tissue samples responses obtained by exposure of the tissue to stimuli and combined processing of tissue responses to each irritant .  11. The method according to claim 1, characterized in that one or more types of tissue of the cervix, breast, skin, prostate or colon are examined.  12. The method according to p. 1, characterized in that the combined processing and comparison of the classified tissue with the classifier is performed in real time and statistical methods are used to compare the classified fabric with the classifier.  13. The method according to claim 1, characterized in that it examines the tissue, which is part of a living organism.  14. The method according to claim 2, characterized in that at least sources of electrical energy and sources of magnetic energy are used as stimuli, the combined processing of tissue responses is carried out by processing the amplitude response, frequency response, absolute amplitude determination, phase response, spectral response, response by the coefficient of the first time derivative or response by the coefficient of the second time derivative.  15. The method according to claim 1, characterized in that at least light energy sources are used as stimuli, and the combined processing of tissue responses is carried out by processing the amplitude response, spectral response or spatial response.  16. The method according to claim 1, characterized in that at least sources of acoustic energy are used as stimuli and the combined processing of tissue responses is carried out by processing the amplitude response, phase response or frequency response.  17. A device for diagnosing a precancerous or cancerous state of the tissue, containing a single probe for exposing the tissue to energy stimuli, sensitive elements, each of which is configured to perceive the tissue response to the corresponding energy stimulus, which is a response energy signal, a controller connected to the sensitive elements to obtain said tissue responses, and comprising a processor for processing said tissue responses and comparing the resulting cut at, and a memory block, characterized in that a single probe for influencing tissue contains many energy sources, and the memory block is configured to store a known classifier of expected types of tissue, the processor is configured to combine processing of tissue responses to each stimulus to classify the tissue and the ability to compare the resulting tissue classification with a known classifier of expected types of tissue for its recognition.  18. The device according to 17, characterized in that the controller contains an indicator for indicating to the user the type of recognizable fabric.  19. The device according to any one of paragraphs.17 and 18, characterized in that the single probe is an operator-controlled probe for contacting the tissue, with energy sources and sensing elements embedded in the probe for examining tissue inside or on the outer surface of a living organism.  20. The device according to claim 19, characterized in that the controller comprises means for identifying the probe with irritation to the tissue for digitally recording each use of the probe and for automatically limiting the number of repeated uses thereof.  21. A device for diagnosing a precancerous or cancerous state of tissue, comprising an electromagnetic radiation source configured to irradiate tissue with electromagnetic radiation of at least two different wavelengths, a single probe connected thereto for transmitting electromagnetic radiation to the tissue and receiving radiation scattered by it according to appropriate at least two different wavelengths, a receiver connected to the probe and a comparison device for comparing tissue responses to electromagnetic radiation which is a scattered tissue response radiation, with known values, characterized in that the probe contains at least one electrode for applying electrical signals to the tissue and its corresponding electrical measuring means for measuring the resulting tissue response to electrical signals, and the comparison device is made with the ability to compare tissue responses to tissue electromagnetic radiation and the resulting tissue response to electrical signals with the corresponding known values and to identify the type of fabric.  22. A method for diagnosing a precancerous or cancerous state of tissue, including exposure to tissue of an irritant in the form of electromagnetic radiation of several wavelengths, followed by processing of tissue responses to electromagnetic radiation, which is a response radiation scattered by the tissue, and analysis of the processed tissue responses, characterized in that electromagnetic irradiation of tissue is carried out by at least two different wavelengths, electrical signals are brought to the tissue with measurement of the resulting response to electrical electric signals combine to process tissue responses to electromagnetic radiation and the resulting tissue response to electrical signals, and tissue diagnostic analysis is performed by comparing the processed tissue responses with the expected tissue responses.  23. The method according to p. 22, characterized in that on the basis of the combined processing of the responses of the tissue carry out its classification and compare the classification of the fabric and the existing classifier of the expected types of fabrics for its identification.

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