RU2596984C2 - Systems and methods for four-dimensional electromagnetic tomographic (emt) differential (dynamic) mixed imaging - Google Patents

Abstract

FIELD: medical equipment.

SUBSTANCE: invention relates to 4D electromagnetic tomographic differential fused imaging. Plurality of electromagnetic field sources and detectors generate and detect an electromagnetic field domain in a target area. Biological tissue is positioned within target area, and an electromagnetic field is generated via a selected plurality of sources. Field is selectively evaluated so that each of a selected plurality of detectors recognises a source of field from plurality of electromagnetic field sources. Sources and detectors are controlled so that fields generated by selected sources are detected by selected detectors after interacting with tissue. Based on field received at each detector, a complex interference matrix is derived from tissue-generated field, and anatomical and functional image information is reconstructed from said matrix.

EFFECT: enabling generation of fused tomographic image displaying functional/molecular information.

21 cl, 29 dwg

Description

LINKS TO RELATED APPLICATIONS

For patent protection purposes in the United States of America, this application is a patent application for the invention and patent claims based on 35 U.S.C. § 119 (e), in relation to provisional patent application in the United States No. 61/362,634, filed July 8, 2010, entitled "SYSTEMS AND METHODS FOR FOUR-DIMENSIONAL ELECTROMAGNETIC TOMOGRAPHIC (EMT) DIFFERENTIAL (DYNAMIC) SOLAR MEMBERSHIP BOTH THIS link. In addition, the entire US patent No. 7239731, issued to Mr. Semenov et al. July 3, 2007 and entitled "SYSTEM AND METHOD FOR NON-DESTRUCTIVE FUNCTIONAL IMAGES AND DISPLAY OF ELECTRIC PERTURBATIONS IN BIOLOGICALLY UNFASTLY incorporated herein by reference.

COPYRIGHT STATEMENT

All materials in this patent application are protected by copyright and related rights laws of the United States of America and other countries. The copyright owner does not object to the facsimile reproduction of the patent application by any person or the disclosure of patent information for reflection in state registration documents, but otherwise all other copyrights are reserved by the owner.

FIELD OF THE INVENTION

The present invention is generally associated with electromagnetic tomography and, in particular, but not exclusively, with four-dimensional electromagnetic tomography to create mixed anatomical and functional images of biological objects.

BACKGROUND OF THE INVENTION

Electromagnetic tomography (EMT) is a relatively new means of obtaining images and has great potential for use for biological and medical purposes, including for non-invasive assessment of the functional and pathological state of biological tissues. The EMT method allows to differentiate biological tissues and, accordingly, to create their image on the basis of differences in the dielectric properties of tissues. The dependence of the dielectric properties of tissues on their various functional and pathological conditions, such as blood and oxygen fullness, ischemic and heart attack injuries, has already been confirmed.

Two-dimensional (2D) and three-dimensional (3D) EMT systems and image reconstruction methods have been developed over the past ten or more years. The possibility of using this technology for various biological and medical purposes has already been proven, for example, in the form of building images of the heart and limbs.

The complexity of the distribution of electromagnetic waves in a scanning chamber: the need to reduce the effect of borders

As in the case of any other creation of biomedical images, the EMT algorithm consists of cycles of measurements of complex signals scattered over the biological object under study, received from a variety of transmitters located at different points around the object, and changed by a variety of receivers located at different points around the object. This is shown in FIG. 1. In other sections of this document, information is provided that the measured typological properties of scattered electromagnetic signals can be used for various methods of creating images by reconstructing the three-dimensional distribution of the dielectric properties of the object, i.e. to create a three-dimensional image of the object.

In general, to create images it is very important to accurately describe the distribution of the electromagnetic field in the scan object. The distribution of the electromagnetic field in the scanning chamber is a very complex phenomenon, even if there is no studied object inside.

There are also problems with borders that arise due to the limited volume of the scanning camera, which should be taken into account or reduced in one way or another.

There are various ways to reduce the impact of physical boundaries. For example, the effect from physical boundaries can be reduced by using absorbent material (or materials) as described in US Pat. No. 7,239,731, or by increasing the absorbing properties of the contrast medium while maintaining a sufficient signal level at the receivers, as described herein (see . section "Module assessment tasks in connection with the attenuation of the signal and the physical boundaries" in FIG. 11).

Recent trends in biomedical imaging: mixed images created by modular systems

Imaging for medical purposes plays a significant role in the development of modern non-invasive diagnostics, treatment planning and monitoring after its completion. Some time ago, the construction of two-mode and multi-mode images began - morphological and anatomical (for example, CT + MRI) and functional (for example, FDG-PET and DCE-MRI). At the same time, the diagnostic efficiency is significantly increased, but with a simultaneous increase in the cost of already expensive medical scanning devices and studies.

The first attempts to combine different methods of constructing images using software showed the presence of significant problems due to the different position of the patient, his movements and involuntary displacement of internal organs. This led to the integration of various scanning modes into a single complex, and not to the combination of images through their processing after scanning. One of the first dual-mode scanning systems, the PET / CT integrated system, was developed at the University of Pittsburgh School of Medicine. The combined PET / CT scanner was designed primarily for the needs of clinical oncology. The first FDA approved serial PET / CT scanner was produced by CTI PET Systems in 2000, and shortly thereafter, GE Medical systems and Philips began production. It is now accepted that the PET / CT scan is much more accurate than just PET in detecting and localizing tumors, and that the PET / CT scan outruns PET in terms of sensitivity, selectivity and accuracy, mainly due to the possibility of detecting new pathological changes. In addition, the combination of PET and CT gives a significant increase in examination time in one session.

After using PET / CT combined scanning, other various combinations of scanning methods appeared. The usefulness of combining SPECT / CT for the needs of cardiology, oncology and neurology has been confirmed. The combination of three-dimensional echocardiography and SPECT myocardial perfusion method was used for stress tests of the heart. The combination of MRI and CT images is used in computer-assisted surgery. The feasibility of using the combined MRI / FDG-PET scan of the whole body of cancer patients has been demonstrated. The authors of one study pointed out that “since some malignant tumors do not have an increased glucose metabolism, the additional information provided by MRI is very useful.”

Subsequently, the combined dual-mode scan turned into multi-mode. Combined multimode morphological (CT and MRI) and functional (FDG-PET and DCE-MRI) scans (combining the three most commonly used clinical imaging methods - CT, MRI and PET) were used to plan treatment, monitor and post-operative monitoring after HF -section of tumors.

There is a fresh trend in the development of medical imaging devices that focus on “working” with specific diseases, such as cancer. This differs significantly from the concept of creating universal systems in the past. For example, one of the reports reported the creation of a PET / CT scanner specifically for diagnosing breast cancer. According to the information in this report, flurodeoxyglucose (FDG) was used as a marker, and the imaging time was 12.5 minutes on one side of the chest.

As indicated above, combined imaging methods significantly improve the quality of diagnostics. However, this increases the already high cost of medical devices. However, integrated imaging systems are very cumbersome and are not intended for use in mobile mode. Accordingly, there is a need for systems, methods and approaches that provide fast, inexpensive, integrated anatomical and functional imaging, preferably in a mobile version.

SUMMARY OF THE INVENTION

According to one or more parameters, this invention is an innovative system for creating four-dimensional (4D) electromagnetic (EMT) images: a three-dimensional spatial image plus a “one-dimensional” image in time, namely a functional one. When creating four-dimensional EMT images instead of combining images obtained by various technical means, the system combines purely anatomical images with dynamic, differential images obtained using the same technology. An innovative concept allows you to create combined functional images of tissues using only fast EMT scanning, which is the key to creating mobile and inexpensive devices. An additional advantage of this concept is the mobility of the EMT system. It is expected that the system will be suitable for “bedside functional scanning” and for inclusion in equipment for resuscitation vehicles or medical aircraft, for example, for use in ambulances or medical helicopters.

In a broad sense of the word, this invention according to one of the parameters is a method of creating functional images and non-invasively assessing the distribution of electrical excitations in biological tissues, including through a variety of electromagnetic field sources to form an electromagnetic field in a given area, a plurality of electromagnetic field detectors to determine at least part of the electromagnetic region in a given region, placing biological tissue in a given region, creating electromagnetic field through a selected set of electromagnetic field sources, selectively determining the parameters of the electromagnetic field generated by each of the electromagnetic field sources so that each of the selected set of electromagnetic field detectors "recognizes" the electromagnetic field source from among the electromagnetic field sources, control electromagnetic field sources and detectors electromagnetic field so that the electromagnetic fields created by the selected set of sources The electromagnetic field was received by the selected set of electromagnetic field detectors after interacting with the biological tissue, measuring the interference parameters of the electromagnetic field caused by at least the electromagnetic field generated by the biological tissue, using at least a portion of the electromagnetic field data obtained by each of the electromagnetic field detectors , determining information for the anatomical and functional image of biological tissue based on measured parameters interference, as well as combining information about the anatomical and functional images to display it as an image.

One of the features of this aspect is that when collecting information to create a functional image, dynamic image data is dynamically obtained, and when combining anatomical image data with functional image data, dynamic anatomical image information is dynamically combined with variable functional image data. In addition, in the framework of this method, a special material is introduced into the biological tissue, the dielectric properties of which are derived with respect to the local electric field created inside the biological tissue, and based on the electromagnetic field parameters obtained at each electromagnetic field detector, the interference parameters are measured electromagnetic field caused by an electric or dielectric object. In addition, in the framework of this method, the generation of the signal is synchronized with the electrical signal characteristic of electrical excitation in biological tissue. In addition, the interference parameters are measured in a complex manner.

Another aspect is that the biological tissue, in respect of which operations such as placement in the scanning area, control, determination of properties, introduction of a contrast medium and both scanning stages are performed, can be heart tissues, and the electrical signal used in the synchronization step, is an electrocardiogram. As part of the development of this opportunity, biological tissue, for which operations such as placement in the scanning area, control, determination of properties, introduction of a contrast medium and both stages of scanning are performed, can be nerve tissues, and the electrical signal used at the synchronization stage, is an electrical signal characteristic of the electrical excitation of nerve tissue. Biological tissue in respect of which operations such as placement in the scanning area, control, determination of properties, administration of contrast medium and both stages of scanning are performed can be skeletal muscle tissue, and the electrical signal used in the synchronization step is an electrical signal characteristic of electrical excitation of musculoskeletal tissue. Biological tissue, in respect of which operations such as placement in the scanning area, control, determination of properties, introduction of a contrast medium and both stages of scanning are performed, may also be biological tissue, and in the framework of the present invention, the method further comprises visualizing the operation of the display by means creating images of functional and pathological conditions of biological tissue, and at least one of the parameters of specific functional s and pathological conditions - filled with blood, ischemia, infarction, hypoxia, malignant tumors, benign tumors, swelling and fever.

Another aspect is that many integrated sources are used to perform scanning - electromagnetic field detectors that generate an electromagnetic field in a given area and detect at least a portion of the electromagnetic field in a given area.

Another aspect is that the sensitive material added before scanning is a composition of many components or nanoparticles, including ferroelectric particles of various sizes. As part of the further development of this feature, at least a part of the ferroelectric particles at the stage of adding a contrast medium is created using strontium-titanium oxide treated with barium, and / or the ferroelectric particles at the stage of adding a contrast medium can have various shapes, including spherical, ellipsoidal or cylindrical.

Another aspect is that the sensitive material added before scanning is a composition of many components, including potentiometric liquid crystals. As part of the further development of this feature, potentiometric liquid crystals at the stage of adding a contrast medium include MBBA, 7CB.

Another aspect is that the sensitive material added before scanning is a composition of many components, including a potentiometric dye. As part of the further development of this feature, the potentiometric dye at the stage of adding a contrast medium includes at least one of the following substances: merocyanine, rhodamine, cyanine, oxonol and a naphthyl-based styryl dye.

Another aspect is that at the preparation stage, the contrast agent is introduced into the biological tissue.

Another aspect is that this method also involves the creation at the preliminary stage of a system for performing the above operations in the format of a mobile land or air vehicle.

Another aspect is that this method also allows you to identify based on the obtained visual information the location of the unhealthy tissue and make a cartogram of electrical potentials in the area of unhealthy tissue to determine the cause of functional impairment or assess the functional ability of this tissue.

In a broad sense, the present invention, according to another aspect, is a functional system for imaging and non-invasively evaluating the distribution of electrical excitations in biological tissues, comprising a plurality of electromagnetic field sources for generating an electromagnetic region in a given region, a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic region in a given area, a working chamber for placing biological tissue in a given area, to a scooter physically connected to a plurality of electromagnetic field sources and electromagnetic field detectors, providing an electromagnetic field generated by a selected plurality of electromagnetic field sources by means of a plurality of electromagnetic field sources and receiving signals by a plurality of selected plural electromagnetic field detectors after interacting with biological tissue, an electromagnetic interference measurement parameter module field caused by at least an electromagnetic field, created by biological tissue, an imaging computer that creates combined anatomical and physiological images of biological tissue and the distribution of electrical excitation in biological tissue by inverting electromagnetic fields detected by many electromagnetic field detectors, as well as a display for graphically displaying the combined anatomical and physiological images of biological tissue.

In this aspect, the imaging computer includes operating units that isolate a dynamic variable functional image and dynamically combine the anatomical image and the variable functional image. In another aspect, a plurality of sources and electromagnetic field detectors and a working chamber are located on a mobile vehicle. Another aspect is that the system also includes sensitive material introduced into the biological tissue, which is characterized in that it has dielectric properties that are a function of the local electric field generated inside the biological tissue, and a module for measuring the interference parameters of the electromagnetic field caused by the electric or dielectric object. Another aspect is that the system also includes a reference module for synchronizing the generation of electromagnetic fields with an electrical signal characteristic of the electrical excitation of biological tissue.

Another aspect is that the biological tissue can be heart tissue, and then the generation of the electromagnetic field is synchronized with the electrocardiogram.

Another aspect is that the biological tissue can be nerve tissue, and then the generation of the electromagnetic field is synchronized with the electrical signal characteristic of the electrical excitation of the nerve tissue.

Another aspect is that the biological tissue can be skeletal muscle tissue, and then the generation of the electromagnetic field is synchronized with the electrical signal characteristic of the electrical excitation of skeletal muscle tissue.

Another aspect is that the graphic display comprises at least one image of a particular functional or pathological state of the biological tissue on which the anatomical and functional image of the biological tissue will be superimposed. In the framework of the further development of this feature, at least one image of a particular functional or pathological state of biological tissue includes an image of at least one of blood, ischemia, heart attack, hypoxia, malignant tumors, benign tumors, edema, and temperature.

Another aspect is that the electromagnetic field source is integrated into a single module with an electromagnetic field detector.

Another aspect is that the sensitive material is a composition of many components or nanoparticles, including ferroelectric particles of various sizes. In the framework of the development of this feature, at least a part of the ferroelectric particles is formed from strontium-titanium oxide treated with barium, and / or the ferroelectric particles can have various shapes, including spherical, ellipsoidal or cylindrical.

Another aspect is that the sensitive material is a composition of many components, including potentiometric liquid crystals. In another embodiment, potentiometric liquid crystals include MBBA, 7CB.

Another aspect is that the sensitive material is a composition of many components, including a potentiometric dye. In another embodiment, the potentiometric dye includes at least one of the following substances: merocyanine, rhodamine, cyanine, oxonol and a naphthyl-based styryl dye.

Another aspect is that the system is located on a mobile land or air vehicle.

According to another aspect, the present invention relates to a method for creating four-dimensional electromagnetic tomographic (EMT) dynamic integrated images of biological tissues, the method includes: providing multiple sources of electromagnetic fields for forming an electromagnetic region in a given area; providing a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic region in a given region; the placement of biological tissue in a given area, generate an electromagnetic field through a selected set of sources of electromagnetic fields; selectively determine the parameters of the electromagnetic field generated by each of the sources of the electromagnetic field so that each of the selected set of detectors of the electromagnetic field "recognizes" the source of the electromagnetic field from the selected set of sources of the electromagnetic field, control the sources of the electromagnetic field and the detectors of the electromagnetic field so that the electromagnetic fields created by the selected set of electromagnetic field sources were received by the selected set of electromagnetic detectors the field after interaction with biological tissue, measure the interference parameters of the electromagnetic field caused by at least the electromagnetic field generated by the biological object, using at least a portion of the electromagnetic field data obtained by each of the electromagnetic field detectors, provide a computer for creating images having a module for evaluating problems related to the dependence of attenuation on physical boundaries, a module for reconstructing images, a module for constructing differential and siderations, movement correction module and a module forming the combined image, and by using a computer to create images for the construction of four-joint anatomical and functional image and outputting them as images.

According to another aspect, using a computer for imaging involves obtaining a dynamic variable functional image, and creating a combined anatomical and functional image involves dynamically combining an anatomical image and a variable functional image. Additionally, the method also includes: introducing into the biological tissue a sensitive material, the dielectric properties of which are a function of the local electric field generated inside the biological tissue, and based on the parameters of the electromagnetic field obtained at each electromagnetic field detector, measuring the interference parameters of the electromagnetic field caused by the electric or dielectric object. In addition, the method further comprises synchronizing the generation of the signal with an electrical signal characteristic of the electrical excitation of a biological object. In addition, the interference parameters contains a complex matrix.

According to the invention, a biological object in respect of which operations such as placing in the scanning area, controlling, preparing, introducing a contrast medium and both scanning stages can be performed can be heart tissue, and the electrical signal used in the synchronization step is an electrocardiogram.

According to the invention, a biological object in respect of which operations such as placing in the scanning area, controlling, preparing, introducing a contrast medium and both scanning stages can be performed can be nerve tissue, and the electrical signal used in the synchronization step is a signal, characteristic of electrical excitation of nerve tissue.

According to the invention, a biological object in respect of which operations such as placement in the scanning area, control, preparation, administration of contrast medium and both stages of scanning are performed can be skeletal muscle tissue, and the electrical signal used in the synchronization step is a signal characteristic of electrical excitation of skeletal muscle tissue.

According to the invention, the method also includes displaying, using means of displaying, plots of specific functional and pathological conditions of biological tissue, and at least one of the parameters of specific functional and pathological conditions can be fixed - blood fullness, ischemia, heart attack, hypoxia, malignant tumors benign tumors, edema and temperature.

According to the invention, the creation of a plurality of electromagnetic field sources and a plurality of electromagnetic field detectors includes the creation of a plurality of integrated sources - electromagnetic field detectors for creating an electromagnetic field in a given area and detecting at least a portion of the electromagnetic field in a given area.

According to the invention, the sensitive material added before scanning is a composition of many components or nanoparticles, including ferroelectric particles of various sizes. According to the invention, at least a portion of the ferroelectric particles in the step of adding a contrast medium is formed using barium-treated strontium-titanium oxide, and / or the ferroelectric particles in the step of adding a contrast medium can have various shapes, including spherical, ellipsoidal or cylindrical.

According to the invention, the sensitive material added before scanning is a composition of many components, including potentiometric liquid crystals. Potentiometric liquid crystals in the step of adding a contrast agent include MBBA, 7CB.

According to the invention, the sensitive material added before scanning is a composition of many components, including a potentiometric dye. The potentiometric dye in the step of adding a contrast agent includes at least one of the following: merocyanine, rhodamine, cyanine, oxonol and a naphthyl-based styryl dye.

According to the invention, the biological object includes biological tissue, and the preparation step includes the introduction of a contrast medium into the biological tissue.

According to the invention, the method also involves the creation at a preliminary stage of a system for performing the above operations in the format of a mobile land or air vehicle.

According to the invention, the method also allows to identify the location of unhealthy tissue based on the obtained visual information and to map the electrical potentials in the area of unhealthy tissue to determine the cause of a functional disorder or assess the functional ability of this tissue.

The present invention according to another aspect is a system for creating four-dimensional electromagnetic tomographic (EMT) dynamic integrated images of biological objects, comprising a plurality of electromagnetic field sources for generating an electromagnetic region in a given region, a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic region in a given region, a working chamber for placing biological tissue in a given area, a controller, an operator Associated with a plurality of electromagnetic field sources and electromagnetic field detectors for generating an electromagnetic field by means of a selected plurality of electromagnetic field sources and receiving signals by a selected plurality of electromagnetic field detectors after the signals interact with biological tissue, a module for evaluating electromagnetic field interference parameters caused by at least an electromagnetic field, created by biological tissue, an imaging computer that creates a united various anatomical and physiological images of biological tissue, including a module for assessing tasks related to the dependence of attenuation on physical boundaries, a module for reconstructing images, a module for constructing a differential image, a module for correcting movements, and a module for generating combined images.

In this aspect, the system also comprises a display for graphically displaying the combined anatomical and physiological images of the biological tissue.

According to the invention, the computer for creating images also includes a module for tuning and testing the EMT system.

According to the invention, the computer for creating images contains a block of know-how.

Another feature of the invention is that the operating modules of the imaging computer dynamically extract time-varying information of the functional image and dynamically combine the anatomical image and the variable functional image, the result of which is the combined anatomical and functional image of biological tissue. Another aspect is that a plurality of sources and electromagnetic field detectors and a working chamber are mounted on a mobile chassis. In another aspect, the system also includes: a sensitive material embedded in biological tissue, the dielectric properties of which are derived with respect to the local electric field created inside the biological tissue, as well as a module for measuring the interference parameters of the electromagnetic field caused by an electric or dielectric object. The system also includes a reference module for synchronizing the generation of electromagnetic fields with an electrical signal characteristic of the electrical excitation of biological tissue.

According to the invention, the biological tissue may be heart tissue, and then the generation of the electromagnetic field is synchronized with the electrocardiogram. Biological tissue can be nerve tissue, and then the generation of an electromagnetic field is synchronized with an electrical signal characteristic of the electrical excitation of nerve tissue. Biological tissue can be skeletal muscle tissue, and then the generation of the electromagnetic field is synchronized with the electrical signal characteristic of the electrical excitation of skeletal muscle tissue.

According to the invention, at least one image of a particular functional or pathological condition, on which an anatomical and functional image of biological tissue will be superimposed, can be displayed as a graphic image. As part of the further development of this particular possibility, at least one image of a specific functional or pathological state of biological tissue can be created, including an image of at least one of the properties - blood fullness, ischemia, heart attack, hypoxia, malignant tumors, benign tumors, edema and temperature .

According to the invention, the electromagnetic field source is integrated into a single module with an electromagnetic field detector.

Another aspect is that the sensitive material is a composition of many components or nanoparticles, including ferroelectric particles of various sizes. According to the invention, at least a part of the ferroelectric particles is formed from barium-modified strontium-titanium oxide, and / or the ferroelectric particles can have various shapes, including spherical, ellipsoidal or cylindrical.

According to the invention, the sensitive material is a composition of many components, including potentiometric liquid crystals. In an embodiment, potentiometric liquid crystals include MBBA, 7CB.

According to the invention, the sensitive material is a composition of many components, including a potentiometric dye. It is possible that the potentiometric dye includes at least one of the following substances: merocyanine, rhodamine, cyanine, oxonol and a naphthyl-based styryl dye.

According to the invention, the system is mounted on a mobile land or air vehicle.

The present invention, according to another aspect, is an imaging computer that creates integrated anatomical and functional images of biological tissues in an EMT system and contains a know-how module, a module for evaluating tasks related to the dependence of attenuation on physical boundaries, a system settings and testing module EMT, image reconstruction module, differential image building module, motion correction module, integrated image generation module, as well as a graphic display displaying the combined images of the anatomical and physiological biological tissue.

Other areas of possible application of this invention will become apparent after reading the detailed description below. The detailed description and specific examples provide an understanding of the most preferred areas of use of the invention, but are provided solely by way of illustration and are not intended to limit the scope of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

Other aspects, applications and advantages of the present invention will become apparent from the following detailed description with reference to the following drawings:

FIG. 1 is a graphical illustration of the principle of electromagnetic tomography (EMT);

FIG. 2 is a schematic representation of an electromagnetic field tomographic spectroscopic system for use in one or more of the most preferred applications based on the invention;

FIG. 3 is a structural diagram of one of the N clusters of the electromagnetic field in FIG. 2 at the moment when the cluster works as a source of waves;

FIG. 4 is a structural diagram of one of the M - modules of the source - detector in FIG. 3;

FIG. 5 is a block diagram of an R-channel module in FIG. 3;

FIG. 6 is a structural diagram of one of the clusters of IF detectors in FIG. 2;

FIG. 7 is a structural diagram of a system for managing electromagnetic field clusters and IF detector clusters in FIG. 2;

FIG. 8 is a block diagram illustrating the integration of a control system in FIG. 6 to the system of FIG. 2;

FIG. 9 is a structural diagram of a cluster of field sources — electromagnetic field detectors in FIG. 3 at the moment when the cluster operates as a wave receiver;

FIG. 10A is a flowchart of a method implemented in an image recreation unit;

FIG. 10B is a flowchart of a method implemented in an image recreation unit;

FIG. 10C is a flowchart of a method of a gradient calculating unit implemented in an image reconstructing unit;

FIG. 11 is a schematic diagram illustrating the use of the system and method shown in FIG. 2-10, as part of a system for constructing four-dimensional differential (dynamic) combined EMT images used as one or more priority applications of the present invention;

FIG. 12 is a photograph of an anatomical cross section of the middle part of the front leg of the pig, which was used to prepare illustrations for experiments in the field of imaging using EMT;

FIG. 13A and 13B are the results of constructing images representing combined images, in a simplified two-dimensional form, of changes in blood circulation, shown as the difference in changes in systolic and diastolic pressure;

FIG. 14A and 14B are the results of constructing images representing combined images, in a simplified two-dimensional form, of changes in blood circulation associated with reperfusion or occlusion;

FIG. 15A and 15B are the results of imaging, which are combined images, in a simplified two-dimensional form, of localized damage detected five minutes (+5) after its occurrence, using the operating frequency of 1.05 GHz;

FIG. 16A and 16B are the results of the construction of images, which are combined images, in a simplified two-dimensional form, of localized damage detected sixteen minutes (+16) after its occurrence, where the operating frequency is 1.05 GHz;

FIG. 17A and 17B are the results of constructing images representing combined images, in a simplified two-dimensional form, of localized damage detected five minutes (+5) after its occurrence, where the operating frequency is 1.5 GHz;

FIG. 18A and 18B are the results of constructing images representing combined images, in a simplified two-dimensional form, of localized damage detected sixteen minutes (+16) after its occurrence, using the operating frequency of 1.5 GHz;

FIG. 19A and 19B are the results of constructing images representing combined images, in a simplified two-dimensional form, of damage caused by a stroke using an operating frequency of 1.0 GHz; and

FIG. 20 is an example of a representative application of functional imaging and non-invasive mapping of electrical potentials using the method according to this invention.

DETAILED DESCRIPTION OF THE INVENTION

It should be noted that any specialist in this field having a general idea of the subject matter will easily understand that this invention has a wide range of applications and potential. In addition, any "preferred" option is considered as part of the most optimal way of use, provided as a tool for applying the present invention. Also, other embodiments may be considered as additional illustrations, which will provide a complete and practical description of the invention. In addition, many embodiments, such as adaptations, variations, modifications, and similar changes will be indirectly disclosed as part of the practical embodiments discussed herein, and they are also included in the scope of the present invention.

Accordingly, although the present invention is described in detail herein as one or more embodiments, it is understood that this information is illustrative, represent examples of the use of the invention and are provided only to provide a complete and practical description of the invention. A detailed disclosure in this document of information regarding one or more practical embodiments is not intended and cannot be construed as limiting the scope of patent protection of this invention, the scope of such protection should be determined by patent formulas and their equivalents. It is not intended that the scope of patent protection be determined by limiting any claims to the provisions of this document that are not directly incorporated into the claims themselves.

Thus, for example, any sequence and / or time sequence of actions in the various processes or methods described herein is illustrative and not limiting. Accordingly, it should be assumed that although actions within the framework of various processes or methods can be shown and described as a certain sequence or time order, actions within the framework of such a process or methods are not limited to performing them in any particular sequence or order if not specified otherwise. In fact, actions as part of such processes or methods can generally be carried out in different order or sequence, but still be part of the present invention. Accordingly, it is assumed that the scope of patent protection of this invention is determined by the attached patent claims, and not by the description given in this document.

In addition, it is important to note that each term used in this document should be understood by a specialist in this field, as the meaning of such a term in the context of its use. If the meaning of any term used in this document (and understood by a specialist, taking into account its context), differs in any way from the specific vocabulary definition of such a term, then it is assumed that the term in which this term should have a priority character understandable to the specialist.

In addition, it is important to note that when used in this document, “any” and “any” generally mean “at least one / one,” and do not exclude the presence of many such objects, unless the context dictates otherwise. Accordingly, the reference to “picnic basket with an apple inside” is a description of a “picnic basket with at least one apple inside” and also “picnic basket with apples inside”. Conversely, the link to "a picnic basket with one apple inside" is a description of a "picnic basket with only one apple inside."

When used as a union word in this document to combine listed items, “or” means “at least one of the items”, but does not exclude the possibility of having multiple items from the list. Thus, the link to “picnic basket with cheese or crackers inside” is a description of “picnic baskets with cheese but no crackers inside”, “picnic baskets with crackers but no cheese inside”, and “picnic baskets and with cheese, and with crackers inside. " And finally, when used to combine the listed items, "and" means "all items from the list." Thus, a link to a “picnic basket with cheese and crackers inside” is a description of a “picnic basket with cheese inside, as well as a picnic basket with crackers inside,” and a description of a “picnic basket with crackers inside, and also picnic baskets with cheese inside. "

Below are considered schemes in which the same numbers denote the same components in different images, and describes priority practical embodiments of the present invention. The following description of one or more priority embodiments is only an example in nature and should under no circumstances limit the nature of the invention, its use or form of use.

FIG. 2 is a schematic representation of an electromagnetic field tomographic spectroscopic system 10 for use in one or more of the most preferred applications based on the invention. In particular, the system 10 of FIG. 2 carries out a functional scan of biological tissues. The system 10 can also be used for non-destructive mapping of the electrical excitation of biological tissues 19 using sensitive (contrast) material (solution or nanoparticles) introduced into the biological tissue 19 or into the circulation system, which are characterized by the presence of dielectric properties, which are manifested depending on the electric field generated biological tissue in an excited state 19, taking into account the priority practical embodiments of the present invention. As shown in FIG. 2, the system 10 includes a working or scanning chamber 12, a plurality of clusters of “sources - electromagnetic field detectors” 26, an equal number of clusters of intermediate frequency detectors (“IF”) 28, and a control system (not shown in FIG. 2), but included in the circuit in FIG. 6. Although only two source clusters are shown — electromagnetic field detectors 26 and two IF 28 detector clusters, it should be understood that a much larger number of those and other clusters can sometimes be used (and ideally should be used), which is sometimes referred to in this document like n .

The scanning chamber 12 should, as far as possible, be a waterproof container of sufficient size so that the human body or one or more parts of the human body can be placed inside. For example, the scanning chamber 12 may have (i) a helmet shape for scanning brain disorders (e.g., acute or chronic strokes) or for creating functional images of nerve tissue, (ii) a cylindrical or other shape for scanning limbs, or (iii) a special shape for breast cancer diagnosis. Accordingly, the camera for scanning can be of various shapes and sizes, and the choice of one or another specific shape or size will be obvious to any person with basic knowledge of the subject. In at least one practical embodiment, the scanning chamber 12 and its clusters of electromagnetic field 26, as well as clusters of detectors IF 28, can be mounted on trolleys so that the corresponding components can be moved as needed, and the trolleys can be locked to ensure stability.

FIG. 3 is a structural diagram of one of the N clusters of the electromagnetic field 26 in FIG. 2 at the moment when the cluster 26 operates as a wave source. In the case of one of the priority embodiments, each electromagnetic field cluster 26 is an operating unit that can function as an electromagnetic field generator (i.e., as an electromagnetic source), or as an electromagnetic field generator, but in the case of other embodiments, the sources and detectors can be separate units. Each cluster 26 is a plurality of source-detector modules 30, one reference channel module (sometimes referred to herein as the “R-channel") 32, and a portion of the distribution blocks 64, 66, and at least two precision attenuators. The number of source modules-detectors 30 (three of which are shown in the diagram) in each cluster of the electromagnetic field 26 can sometimes be referred to as M in this document. In general, the more the source-detector 30 modules are used, the faster and more accurate will the system 10 work. The number of source-detector 30 modules can be optimal when their number corresponds to the number of antennas. With regard to practical application, the issues of production capability, convenience and downsizing of the system, including issues of its mobility, are subject to further evaluation.

In FIG. 4 shows a block diagram of one of the M - source modules - detectors 30 in FIG. 3. Each detector source 30 includes a BPSK (binary phase shift keying) modulator 34, an amplifier 36, a direct isolation device 38, a switch 40, a low noise amplifier (“LNA”) 42, a mixer 44, a programmable voltage amplifier (“PGA”) 46, and antenna 48. The switch 40 is used to connect the antenna 48 to the system 10 as a source of an electromagnetic field or an electromagnetic field detector. When connected as a source (i.e., when the switch 40 is in the lower of the two positions shown in FIG. 4), the input signal from one of the distributed blocks 64 (as shown in FIG. 3) is modulated by a BPSK 34 modulator, amplified by an amplifier 36 and is broken by a direct decoupling device 38 before passing through the switch 40 to the antenna 48. And vice versa, when connected as a detector (that is, when the switch 40 is in the upper of the two positions shown in FIG. 4), the signal received by the antenna 48, passes through switch 40 on the LNA 42, where it is amplified and then mixed with a reference signal supplied by the second distribution block 66 (as shown in FIG. 3), and then amplified once again by the PGA 46.

In FIG. 5 shows a block diagram of an R-channel module 32 in FIG. 3. As indicated above, there are many ( M ) modules of source-detectors 30 in each cluster of the electromagnetic field 26, but there is only one R-channel module 32. The R-channel module 32 includes a switch 50, an adder 52, a direct decoupling device 54, an LNA 56, a mixer 58, and a PGA 60. The switch 50 controls the state of the R-channel 32 module whether it works as a source or as a detector. When the R-channel module 32 operates as a source (i.e., when the switch 40 is in the upper of the two positions shown in FIG. 5), the output signal from the source-detector modules 30 passes through an adder 52 and a direct decoupling device 54, and amplified by the LNA 56 before mixing it with the reference signal and then amplifying the PGA 60. And vice versa, when the R-channel module 32 works as a detector (that is, when the switch 40 is in the lower of the two positions shown in FIG. 5), the reference the signal passes directly to the source-detector modules 30, where it combined with signals received by the corresponding antenna 48.

FIG. 6 is a structural diagram of one of the N clusters of IF detectors 28 in FIG. 2. Each cluster of detectors IF 28 includes a family of digital correlation detectors M + 1 70 for working with test signals M (one from each module of source-detectors 30 in the corresponding cluster of electromagnetic field 26) and a signal of one reference channel. These digital detectors 70 allow the information / working frequency of the signal to pass on a selective basis, with clipping interference. Each IF 28 detector cluster also includes a cluster management module, bus, and power supply.

FIG. 7 is a structural diagram of a control system for clusters of electromagnetic fields 26 and clusters of detectors IF 28 in FIG. 2. The control system includes a control computer 14, an imaging computer 15, a synchronization unit 16, a support module 18, a distribution network 20, a calibrator 22, and a power source 24. The control computer 14 controls the overall system operation, data acquisition, tuning, and calibration system, and also transfers all the raw data to a computer to create images 15 for subsequent data inversion and image construction. As the control computer 14, a conventional household computer can be used, for example, a modern Intel-based computer with an RS-488.2 port and corresponding system management software. The synchronization unit 16 is a module that includes a system administrator program and a system hub. Together they provide data exchange with the control computer 14 (preferably via USB 2.0 or Firewire) and with the control units of various clusters 26, 28, and also allow you to synchronize the operation of the system.

The support module 18 includes two generators, one or more thermostats for temperature stabilization of the operation of the reference channels, a BPSK modulator for phase modulation, power dividers, attenuators and similar equipment. Two generators are high-precision unmodulated signal generators: Carrier _ref and LO _ref . Management and configuration of these generators are carried out from the control computer 14 through the interface. Distribution network 20 is a switching module for receiving the carrier and local oscillator reference signals ( Carrier _ref and LO _ref ), as well as the reference signals Rr and Rtr ( Rr _ref and Rtr _ref ) from the reference module 18 and for distributing signals to each of the electromagnetic field clusters 28.

Calibrator 22 is used to calibrate and fine tune the system 10. Calibrator 22 includes a calibration signal source, one or more (preferably two) antennas for calibration, high-precision drives, and one or more (preferably three) calibrated layouts. Calibration antennas and mock-ups can be precisely mounted at any point inside the scanning chamber 12 using high-precision positioning drives. 24 isolated power supply provides reliable system power. One suitable power source for use with the present invention is a three-phase 10 kVA 190/380 AC power supply. The exact requirements for the power supply 24 will depend on the parameters of the power networks in the country in which the system 10 is planned to be used.

FIG. 8 is a block diagram illustrating the integration of a control system in FIG. 6 to system 10 of FIG. 2. Each cluster of the electromagnetic field 26 is located next to the scanning camera 12 so that the antennas 48 are located on or near the surface of the camera 12. The conclusions of the modules of the source-detectors 30 and the module of the R-channel 32 of each of the clusters of the electromagnetic field 26 are connected to the corresponding cluster detectors IF 28, and each cluster of detectors IF 28 is connected as a corresponding cluster of the electromagnetic field 26, and with the synchronization unit 16. The inputs of each cluster of the electromagnetic field 26 are connected to the distribution network 20. Distribution network 20 includes at least four distribution blocks 68, which can be 34-channel power dividers, and a system bus for distributing various reference signals ( Carrier _ref , LO _ref , Rr _ref and Rtr _ref ) to electromagnetic field clusters 26. As shown in FIG. 7, one set of all four signals is sent to each cluster of the electromagnetic field. These signals are denoted as Carrier _i , LO _i , Rr _i and Rtr _i , and then Carrier ₁ , LO ₁ , Rr ₁ and Rtr ₁ are supplied to the first cluster of electromagnetic field 26, and to the second cluster of electromagnetic field 26 (not shown separately) signals Carrier ₂ , LO ₂ , Rtr ₂ and Rtr ₂ , and so on. Finally, as described separately, the signals Carrier _ref and LO _ref are supplied to the distribution network 20 using the reference module 18.

During use, the scanning chamber 12 may be filled with one of a variety of solutions or gels 17, selected taking into account the properties of the tissues of the biological object 19 under study, so as to ensure biological compatibility with it. Acceptable solutions 17 include, but are not limited to, water, salt solutions, sugar solutions, fatty emulsions, solutions based on a mixture of alcohol and salts, and the like. These solutions can also be used as gel components. Sensitive material (solution) can be pumped into the studied object 19 (or the solution can be distributed over the object 19 using a circulation system), the dielectric properties of which depend on the local electric field created inside the excited biological tissue 19, so that the data such dielectric properties could be restored using microwave (electromagnetic) tomography. It is desirable that the injected materials or solutions be multicomponent materials with ferroelectric particles in their composition, such as barium-treated strontium-titanium oxide, and that they have a different shape, including spherical, ellipsoidal, cylindrical or otherwise, for certain applications . In at least some practical embodiments, one or more materials for injection include complex functionalizing nanoparticles (NPs). Separate functionalizing NPs may also contain ferromagnets, biocompatible shells designed for specific biological environments, as well as the required means of drug delivery. Materials or NPs can also selectively include potentiometric dyes, such as merocyanine, rhodamine, cyanine, oxonol and a naphthyl-based styryl dye, and / or selective potentiometric liquid crystals, such as MBBA, 7CB.

The studied object 19 is placed inside the scanning chamber 12, after which the system 10 is activated. During operation of the system 10, each Carrier _i signal from the signal generator in the reference module 18 is directed to the source-detector module 30, which operates in the source mode, as shown in FIG. 3 and 4, where it is modulated with a phase shift (in the case of a phase shift) based on a pseudo-random algorithm so that it is possible to distinguish individual transmit antennas 48 or sources from each other 48, which transmit simultaneously. As described previously, the resulting signal is then amplified before passing through the direct decoupling device 38 to the antenna of the corresponding source 48. Accordingly, an electromagnetic field of incident radiation (“ E _inc ”) corresponding to a specific antenna 48 or channel is formed next to the studied object 19. In addition, part of the signal creating the field E _inc is separated and transmitted to the receiver in the module of the R-channel 32 (one for each cluster of the electromagnetic field 26). In the R-channel module 32, this signal is mixed with the reference signal Rr _i . By further comparing the resulting signal data with the parameters of a known signal, the properties of E _inc can be precisely determined, as described below.

After interacting with the studied object 19, each “distorted” or scattered electromagnetic field (“ E _sct ”) is determined using the corresponding antenna 48, operating in the signal reception mode. FIG. 9 is a structural diagram of a cluster of sources - electromagnetic field detectors 26 in FIG. 3 at the moment when the cluster operates as a wave detector. The same reference signal Rr _i described in the previous paragraph is supplied to the detector sources 30 in the electromagnetic field cluster 26 (operating in detector mode), which are next in turn after the receiving antenna 48. This allows the signal Rr _i from the R channel ( the exact parameters of this signal are known) to pass through all parts of the detector 30, through which the signal E _sct also passes. Accordingly, mixing the R-channel signal into the measurements carried out by the source-detectors 30 both in the sending and receiving modes, can significantly reduce the interference caused by the temperature and temporary instability of the electronic components of the channel.

Data and other information collected by the system 10 are sent to a computer for imaging 15, in which calculations are performed to solve the inverse tomography problem based on the electromagnetic field. The solver can be or include, for example, a solver of three-dimensional vector problems (“3D”) in an un simplified formulation using Maxwell's equations, or a solver of 3D scalar problems in a simplified delivery, or a solver of 2D scalar problems in an even more simplified formulation. FIG. 10A, 10B, and 10C are flowcharts of this process. In the framework of this method, a repeating procedure is used, based on either gradient or Newtonian equations, or a simplified version is used based on the Born-Rytov approximation. If a non-approximating method is used, then it should, if possible, have one or more of the following characteristics: (i) the method should be based on minimizing the difference between typical scattering fields and measured scattering fields; (ii) the Tikhonov regularization method should be used; (iii) one of the types of calculation grids should be used; (iv) one step of the iterative procedure should be the solution of two sets of direct problems of the same order: modeling i.e. “direct wave” and “backward wave” modeling; (v) both the forward and backward waves must be calculated with reference to the non-reflective or metallic boundaries of the object; (vi) both the forward and backward waves must be calculated on a single rectangular grid; (vii) the conjugate gradient method (“CGM”) can be used to solve the direct problem; (viii) at one stage of the CGM, the sine Fourier transform must be used; and / or (ix) the wave equation for heterogeneous media should be used to solve the direct problem.

From a mathematical point of view, the methodology used for tomography based on an electromagnetic field is a solution to the inverse problem. It can be described on the main complex dielectric properties of ε and / or magnetic properties of μ and electric and magnetic fields - E , H. The basis is a set of Maxwell equations, as shown in US 7239731 (equation 1), where E and H mean electric and magnetic fields, respectively, and all other notations are standard.

From a practical point of view, it seems reasonable to rewrite these equations in the form of equations for an inhomogeneous wave, as shown in US 7239731 (equation 2), where

k ² = (2π / λ) ² εμ,

butλ -wavelength in vacuum. A tomographic scanning system based on an electromagnetic field can be schematically represented as a camera with antennas on its surface. As discussed above, some antennas function as electromagnetic field sources, while others function as electromagnetic field detectors. It seems useful to split the electric fieldE on the field of incident radiationE ₀ and scattered fieldE _sas shown in US 7239731 (equation 3), wherej - number of a specific transmitter or source. Equation 2 can be rewritten in the form in which equation 4 is given in US 7239731, wherek ₀ ²is the wave number for a homogeneous object, andE _0j - field created by antenna numberj.

An object can be described as the distribution of permittivity in a scan field.

The receiving antenna and the electronic unit of the receiver detect a complex signal (for example, its amplitude and phase), which reflects both the field of the incident radiation and the scattered field.

In order to solve equation 4, we need boundary data in order to limit the scope of the calculations. For this purpose, you can use both data on non-reflecting and reflecting (metallic) boundaries of the object. The interaction of electromagnetic fields with the antenna is solved as a separate task.

Antenna Models

In specific applications, the magnitude of the fields of the incident radiation is an important component of the reconstruction algorithm. Using the finite time difference method (FDTD), it was found that for a transmitter with a rectangular waveguide (one of the antenna variants), the field distribution can be described as the Kirghof vector integral with the cosine distribution of the electric field along the edge of the antenna, as shown in equation 5 in US 7239731. Equation (5) is confirmed by experimental results. The same type of antenna can also be used as a receiver. To describe the process of recording a signal, the principle of reciprocity can be used. It gives various forms of expression of the recorded signal. Two forms are used in our calculations. First, the value of S _ij can be calculated using equation 6 in US 7239731, where S _ij is the signal received at the antenna number i in the situation when the antenna number j works as a transmitter or source, C ₁ is a constant, E _i means distribution of the electric field created by the receiving antenna, E _j means the distribution of the electric field created by the source antenna, Δε is the distribution of the dielectric constant of the object, and the integral is taken in the region V where the object is located. Equation 6 is used to solve the inverse problem given in equation 7 of US 7239731, where the integral is distributed over the surface of the region.

Direct Problem Solving Unit

To solve direct problems, a method of conjugate gradients with preliminary processing can be used. For this, equation (4) can be rewritten in the form given in equation (8) in US 7239731, where k _av is the average value of k . The precondition operator can be constructed as the first step of the iterative process shown in equation (9) US 7239731. Given the fact that the left side of equation (8) is an expression with a constant coefficient, equation (9) can be solved in step 1075 using sinusoidal Fourier transform for the case with zero boundary conditions along the boundary of the calculation domain. Then the method of R.A. James (originally invented for static problems, but subsequently developed for electromagnetic problems) so that the boundary conditions are not reflected. This technique creates a very reliable and efficient way. Computational experiments show that the iterative process works with any reasonable contrasts and ensures that non-reflective conditions are taken into account with a very high degree of accuracy. Using the sinusoidal Fourier transform at step 1075 can speed up the calculations by eight times than with the standard Fourier approach.

In FIG. 10A is a flowchart of a direct recreation process solver part 1035 of the image reconstruction process. Direct Problem Solver 1035 is used only to solve the inverse problem. The input data in this case is the distribution of dielectric properties in the form of a three-dimensional array, which is obtained at step 1060. For the first stage of iteration, these input data are obtained from an external source, and at subsequent iterations they are obtained from the previous iteration. Next, at step 1065, parameters and arrays are prepared that do not change in the process of solving direct problems: the number of waves, computational grids, and also the Green function for a uniform region. After that, the iterative procedure of conjugate gradients is carried out at steps 1070 and 1080. First, the initial term of equation (4) is calculated at step 1070. Then, each step of the method of conjugate gradients requires fast Fourier transforms of the original functions, as shown in step 1075. To do this to terminate the iteration, the convergence of the process is checked at step 1080. Once the iterative procedure is completed, non-reflective boundary conditions must be applied at step 1085. Finally, a calculation result is generated during process 1035 at 1090. The result includes arrays containing electric fields within the computational domain, and signals at the receivers for all transmitter positions.

Inverse problem solving block

To solve the inverse problem in microwave (electromagnetic) tomography, the gradient method or the Newton method can be applied. In the case of a three-dimensional vector in cylindrical geometry, this method needs significant modifications in comparison with two-dimensional and scalar cases. In general, the inverse problem in electromagnetic tomography can be formulated as the minimization problem shown in equation (10) in US 7239731, where S _ij ^theor are the theoretical values of the signal, S _ij ^exper are the experimental values of the signal, and the last component is the functional Tikhonov.

An important point of any minimization procedure for methods based on gradients is the method of calculating the gradient itself. It was proved that the functional gradient in our case is calculated by equation (11) US 7239731, where E _j and G _ij are the solutions of equations (12) and (13) in US 7239731. The functions F _j and P _ij describe field diagrams for antennas 48 which are used as sources and detectors, respectively.

Direct calculation using equation (11) takes a very long time even for two-dimensional cases and cannot be effectively applied in the three-dimensional case. The reason for this is that at each stage, solving N × M direct problems is required, where N is the number of transmitters and M is the number of receivers. In the previous “scalar” solution, it was shown, and in the case of a vector solution, a generalization can be made that the function shown in equation (14) in US 7239731 can be a solution of equation (15) US 7239731. As a result, at each stage of the iteration, it is necessary to solve only two direct tasks.

The calculation of the sum on the right side of equation (15) remains a difficult task, since it requires summation over all receivers for all cells of the computer network. To overcome this obstacle, a two-step procedure can be applied. First, equation (16) in US 7,239,731 can be calculated over the surface of the computational domain. This requires significantly lower computational costs compared with the calculations on the right side of equation (15). Secondly, equation (17) in US 7239731 can be solved with the specified boundary conditions. Equation (17) is an equation with constant coefficients and can be easily solved using a sinusoidal fast Fourier transform.

Finally, one step of the gradient method requires solving two direct problems (equations (12) and (15)) plus one equation (equation (17)) with constant coefficients. In general, this procedure seems to be the fastest known procedure.

One step of the iterative procedure can be performed as shown in equation (18) in US 7239731, where the iterative step is selected by the sample method. Restrictions on the upper and lower boundaries of the values of dielectric properties and values of dielectric properties along the boundary of the object are applied at this stage.

In FIG. 10B is a schematic diagram of a portion of an inverse problem solver 1000 during image reconstruction when a gradient method and / or Newton method is applied. At 1005, input data is obtained. The input data for the inverse problem solver 1000 includes the physical and geometric parameters of the computational process: dimensions of the computational domain, operating frequency, maximum number of iterations and signals from antennas 48. Next, at step 1010, the preparation of parameters and arrays that do not change during the process iterations when solving inverse problems. Such parameters may include, but are not limited to, the number of waves, computational grids, as well as the Green's function for a uniform region. After that, an iterative procedure for calculating the gradient of the residual function (equation (11)) and / or matrix inversion (for methods based on the Newton method) is performed at step 1015. In order to stop the iteration, the convergence of the process is checked at step 1020. This includes comparing the value of the residual error with the calculated error of the experiment. Once the iterative procedure is completed, non-reflective boundary conditions should be applied at step 1025. Finally, the calculation result in process 1000 is created at step 1030. The result includes the distribution of dielectric properties in the form of a two-dimensional and three-dimensional array.

FIG. 10C is a schematic diagram of a gradient calculation block 1015 in the process of image reconstruction; the direct wave is calculated in step 1035 by equation (12), after which, in step 1040, the source of the back propagation wave along the boundaries of the computational domain is calculated by equation (16). Then, at step 1045, the back propagation wave source is calculated in the computational domain volume by equation (17), and the back propagation wave is calculated by solving equation (13) in step 1050. Finally, the gradient is calculated by equation (11) in step 1055.

The image reconstruction algorithm, which is the subject of this invention, has many advantages. For example, by using non-reflective boundary conditions plus a sinusoidal fast Fourier transform, the direct problem solver of this invention is the most effective. In addition, the proposed method for calculating the so-called backward wave (equations (15), (16), (17)) allows you to work in a real three-dimensional configuration with multiple antennas. In addition, the method of calculating the signal (equation (7)) is different from any others and allows you to simulate the operation of each antenna with a high degree of accuracy, and the mathematical algorithm itself is essentially parallel, which has special advantages for parallel calculations.

FIG. 11 is a schematic diagram illustrating the use of the system 10 and the methods shown in FIG. 2-10, as part of a system for constructing four-dimensional differential (dynamic) combined EMT images 100, used as one or more priority practical embodiments of the present invention. In this application, ε * means a complex number, unless otherwise indicated. The system includes a “know-how unit” 102, a “module for evaluating tasks in connection with signal attenuation and physical boundaries” 104, a module for tuning and testing the EMT system "106," a module for reconstructing images "108," a building module differential image "110," motion correction module "112 and" combined image forming module "114.

As shown in the lower right corner, two important input factors of the method and system are the type of imaging study and the duration of the study ( T_study ). A type of imaging study can be, for example: i) a dynamic study of normal physiological activity in the soft tissues of a limb or myocardial tissue or brain tissue, ii) a controlled stress study to assess the functional viability of tissues (e.g. myocardium or muscle tissue) during physical stress ( training) or pharmacologically induced stress (for example, using dobutamine during an already approved clinical procedure), iii) the introduction of electromagnetic contrast a gent (s) (for example, synthesized from composite functional nanoparticles), or a similar substance, or be a combination of the above types. The duration of the study ( T_study ) may be an introductory factor, for example, in seconds or in the number of cycles of physiological activity (for example, cardiac cycles).

Based on the introductory factor, the system calculates, as represented by the know-how block 102, various desired system parameters. These parameters preferably include the necessary time resolution (time intervals between each cycle (frame) of EMT data acquisition), the number of frames that must be received by the system, the necessary accuracy of measurements in amplitude, the necessary accuracy of changes in phase, and also the necessary accuracy changes in polarization (if necessary).

Using this information, the “task evaluation module due to signal attenuation and physical boundaries” 104 calculates i) the optimal dielectric properties ( ε * ₀ = ε ' ₀ + jε " ₀ ) of the corresponding solution (the scanning chamber is filled with the solution), mainly by optimization the signal attenuation component ( ε " ₀ ), and ii) the bandwidth of the intermediate frequency of the system based on the required time resolution and the number of system channels that need to be obtained. An appropriate solution is then prepared by mixing water, alcohol and salt or other components, as described above, in the required concentration corresponding to the desired dielectric properties ( ε * ₀ = ε ' ₀ + jε " ₀ ). The working or scanning chamber 12 can then be filled such a solution.

Using the "module for tuning and testing the EMT system" 106, the system 100, including the EMT system 10, is adjusted and brought to its original position, and after filling with the solution, a test can be performed using the "empty" camera, i.e. however, the chamber 12 is filled with an appropriate solution, but there is no research object 19 or solution or gel 17 inside. This makes sure that the system has the desired parameters.

When the system 100 is ready, the test object 19 is placed in the scanning chamber 12, together with the solution or gel 17, and a complete set of EMT data (frames) is obtained, as described above, at each time point T0 , T1 ... T_study . Primary EMT data for each moment of time is supplied to the image reconstruction block 108 for calculating the absolute anatomical image at each time interval T0 , T1 ... T_study . The absolute anatomical image, which is determined at the moment T0 , which is sometimes referred to as the "Original Image", is used to calculate the differential image and the combined images at all further time instants T1 ... T_study . For frame T0, the initial moment (the initial distribution of dielectric properties in the region whose image is obtained) for the iterative image reconstruction procedure can be the uniform distribution of the corresponding solution ε * ₀ = ε ' ₀ + jε " ₀ within the region whose image is obtained. For all others frames ( T1 ... T_study ), the initial moment may be the uniform distribution of the corresponding solution ε * ₀ = ε ' ₀ + jε " ₀ within the region, the image of which is obtained (Original image ( ε * _{frame T0} )), or, as Alternatively, the starting point may be the reconstructed image from the previous frame. In other words, the original image ( ε * _{frame T0} ), which is the reconstructed distribution of dielectric properties at the time T0 , can be used as a starting point for reconstructing the image at other time instants (frames) T1 ... T_study , or alternatively , the image reconstructed at the time Ti ( ε * _{frame Ti} ) can be used as a starting point for reconstructing the image in frames i + 1 , i + 2 , etc. This greatly speeds up the process of image reconstruction by reducing the required number of iterations.

The "differential image building module" 110 calculates differential images between the original frame T0 and the current frame Ti as follows:

ε * _diff = (ε * _{frame Ti} -ε * _{frame T0} ) / ε * _{frame T0} × 100 [%]

It is highly desirable that the reconstructed images at moments T0 and Ti be still. Despite the very short time it takes (preferably, about ten milliseconds or less), a movement adjustment may be required. This can be done in the "motion correction module" 112.

The combined image at each point in time Ti can be obtained through the "combined image forming module" 114. As one of the options, the background image, which is the absolute anatomical image of the biological object 19, is created using gray scale, and the time-differential image created using color gamut, superimposed on the background image. In an absolute anatomical image, bone regions having low dielectric properties can be transmitted using darker shades of gray, and soft tissues can be transmitted using lighter shades of gray. In a time-differential image that reflects physiological activity or interventions during the study, the degree of change can be transmitted, as shown in the color bar as a percentile of the change. Simple examples of such combined images obtained during preliminary experiments using the above systems and methods described above are given below.

Examples: Middle part of the front leg of the pig

To verify the methodology described in this application, experiments were conducted using part of the middle part of the front leg of the pig. FIG. 12 is a photograph of an anatomical cross section of the middle part of the front leg of the pig, which was used during these experiments.

One series of experiments focused on changes related to blood circulation, including a comparison of changes in systolic and diastolic pressure and a comparison of reperfusion and occlusion . FIG. 13A and 13B and FIG. 14A-14B are the results of constructing images representing combined images in a simplified two-dimensional form, changes in blood circulation in case of changes in systolic and diastolic pressure, as well as changes in blood circulation in case of reperfusion and occlusion, respectively; On each pair of results, the result of the image at the top is the combined image of ε ' , and the result of the image at the bottom is the combined image of ε . " Newton's iterative method was used to reconstruct the 2D image. Reconstructed absolute anatomical images (background image shown in gray color gamma) are well correlated with anatomy (as shown in FIG. 2) and they clearly visible bone region having low dielectric properties (dark ttenki gray), and soft tissues having a high dielectric properties (lighter shades of gray). While these experiments, the reconstructed values of the dielectric properties are beyond the expected / tabular properties of tissues, at least one additional study showed the possibility of a more exact reconstruction of the absolute values of dielectric properties even with a noise factor of 5-10%. The task is mainly characterized by the complexity and the need to optimize it.

In each combined image, the highlighted area indicates the degree of physiological change that occurs as a result of interference with soft tissue, expressed as a percentage. In FIG. 13A-13B, which correspond to changes in blood circulation for the case of systolic-diastolic pressure, this indicator is calculated as (ε_systolic -ε_diastolic)/ ε_diastolic (expressed as a percentage), and in FIG. 14A-14B, which correspond to changes in blood circulation for the case of reperfusion and occlusion, this indicator is calculated as (ε_reperfusion -ε_occlusion)/ ε_occlusion (expressed as a percentage). The existence of such changes in ε 'and ε "that have arisen due to physiological changes resulting from an intervention in soft tissue has been established previously.In at least one study conducted by one or more of these inventors, there were differences in the measured electromagnetic fields of up to 10-20% in amplitude and 4-6 ° in phase, which were recorded only on two or three receivers out of a maximum of thirteen receivers in the experimental system (for a specific configuration of transmitters / receivers). Better results can be expected if more receivers are used per measurement area.

Differential time images combined with anatomical ones shown in FIG. 13A-13B and FIG. 14A-14B, indicate changes associated with blood circulation, while they correspond to the anatomical location of blood vessels. The percentage of changes was small, within 1% on ε ' and 2-3% on ε " . In this regard, it should be understood that in the microwave tomography reconstructed average dielectric properties above a certain value. In this case, blood vessels are included along with part of the skeletal muscles In the early experiments without imaging and in computer simulations, the inventors suggested that despite the fact that the MW technology is at an early stage of its development, it is estimated that this technology will enable struction of changes in the amount of approximately 3-5% of the total cross-flow. Additional studies to examine the relationship between the changes in blood flow in the limbs and differential values of the reconstructed image. This will directly apply this advanced technology imaging can be performed.

Another series of experiments was devoted to the development of a simulated pig pressure syndrome.In one of the experiments, the MVT 100 system was applied tofrequency of 1.05 GHz, and in the course of another - system 100 was applied at a frequency of 1.5 GHz. FIG. 15A-15B and FIG. 16A-16B are the results of imaging, presented in the form of combined images, in a simplified two-dimensional form, of the syndrome of increased pressure of localized damage identified five minutes (+5) and sixteen minutes (+16) after its occurrence, respectively, using operating frequency of 1.05 GHz. FIG. 17A-17B and FIG. 18A-18B are the results of imaging, presented in the form of combined images, in a simplified two-dimensional form, of the syndrome of increased pressure of localized damage identified five minutes (+5) and sixteen minutes (+16) after its occurrence, respectively, using operating frequency 1.5 GHz. On each pair of results, the result of the image above is a combined imageε ', and the result of the image below is a combined imageε ". Newton's iterative method was used to reconstruct the 2D image. As in the experiments with changes related to blood circulation, the reconstructed absolute anatomical images (the background image shown in gray) are well correlated with the anatomy (as shown in FIG. 2) and the bone region having low dielectric properties is clearly visible on them ( dark shades of gray), and soft fabrics with higher dielectric properties (lighter shades of gray).

In each combined image, the color-highlighted area indicates the degree of physiological change associated with the development of a simulated high blood pressure syndrome, expressed as a percentage. The change value is calculated as (ε_+ x min from the moment of increased pressure -ε_ source)/ ε_initial (in percent). As in the case of changes associated with blood circulation, the existence of such changes in ε 'and ε "was established earlier. However, the general differences associated with the development of a simulated syndrome of high blood pressure in the limbs of an animal are much more significant: up to six times in amplitude and up to 150 ° in phase 16 minutes after the development of the syndrome. This indicates a confident reconstruction of the image showing the location and extent of damage in the soft tissues of the limb.

Differential time images combined with anatomical ones shown in FIG. 15-18, indicate changes in the limbs associated with the development of a simulated pressure increase syndrome, and correspond to the anatomical location of the intervention. More specifically, the images show that there has been an expected accumulation of additional fluid, indicated by distinct blue to red portions of the differential image. At the moment, the inventors have not been able to methodologically perform MW experiments, while simultaneously tracking local pressure as an independent marker of damage. However, a visual examination showed clear signs of a tumor. In addition, after direct injection of Ringer's solution into the muscular section, a decreased arterial blood flow (by 20%) was observed, which indicates an increase in local pressure.

The percentage change in the experiments is significant. For example, in the case of a simulated local pressure increase syndrome presented in FIG. 15A-15B and FIG. 16A-16B, the maximum changes 5 minutes after the development of damage (FIG. 15A and 15B) are about 20% for both ε ' and ε " (blue), while 16 minutes after the onset of damage ( FIGS. 16A and 16B) the maximum changes are much larger, about 38% for ε ' and about 100% for ε " (red). It should be borne in mind that in this case the frequency of 1.05 GHz was used; in General, the changes are more localized and more pronounced, especially at ε ", at higher frequencies, as can be seen when comparing FIG. 17A-17B and FIG. 18A-18B, where the operating frequency was 1.5 GHz, with FIG. 15A -15B and FIG. 16A-16B.

Examples: Two-dimensional computer model of the head

The initial applicability of the new concept of obtaining images using an electromagnetic field for obtaining images of the brain was evaluated using a two-dimensional computer model of the head.

FIG. 19A and 19B are the results of constructing images, which are combined images, in a simplified two-dimensional form, of damage caused by a stroke, using the operating frequency of 1.0 GHz. During this experiment, two small (with a radius of 1 mm) inhomogeneities with dielectric contrasts of -10% and + 10% were added to the model to simulate small sections of a stroke of various nature. The result of obtaining the image at the top (FIG. 19A) is the combined image of ε ' , and the result of the image at the bottom (FIG. 19B) is the combined image of ε . ”The background images in gray colors are absolute images of the head model. Absolute images were recreated using nonlinear Newtonian inversion of scattered electromagnetic fields from 64 receivers located at the same distance from each other in a circle (radius = 11 cm) around the head. of the different images shown in color. Differential images were obtained on the basis of differences between the two reconstructed absolute images: images of a normal head and images of a head with two small sections of excellent blood circulation simulating two types of strokes. As can be seen in FIGS. 19A and 19B, two small (1 mm radius) sections of the stroke are clearly defined.The obtained results demonstrate the applicability of the technology not only for quick assessment of damage in as a result of a stroke, but also indicate the huge potential for obtaining functional neuroimages as an alternative to functional MRI, which is clearly much more progressive in terms of time resolution.

FIG. 20 is an example of a representative application of functional imaging and non-invasive mapping of electrical potentials using the method provided by this invention. It is demonstrated that the system and methodology of the present invention allow both obtaining functional images of biological objects 19 and mapping electrical excitation in biological tissues 19. This can be achieved as a result of a two-stage image acquisition process, as shown in FIG. 20. Firstly, the system 100 is used as a tool for obtaining electromagnetic tomographic images for a non-invasive assessment of the functional and pathological conditions of a biological object 19 and the location of areas of unhealthy tissues 19. For example, in FIG. 20, a functional image of heart tissue was obtained with suspicious myocardial sites in Step 1 to identify areas of ischemia / heart attack. Secondly, if the unhealthy area is within the biological tissue 19 in which the excitations were caused (such as heart tissue, nerve tissue, musculoskeletal tissue or similar types of tissue), then the dielectric contrast (sensitive) substance / solution (for example, suspension nanoparticles) can be introduced into the tissue (circulatory system), which will allow for non-invasive mapping of electrical excitation and determine the location of the source of disturbance (source of arrhythmia). Since the functional / pathological state of the tissue in and near the source is known from the results of the first stage of image acquisition using an electromagnetic field, it becomes possible to obtain unique and very valuable information that will be obtained to determine tissue viability and select a strategy for further treatment and therapy. For example, in FIG. 20 electrical potentials at ischemia / heart attack sites in the heart tissue are mapped to identify possible sources of arrhythmia and functional viability of the tissue. In addition, if a method of removing such tissue is selected, the same system can be used and electromagnetic energy can be focused specifically on a given area according to known methods, such as those described in US Patents Nos. 5715819, 6026173 and 6333087, each of which is included in this application by reference.

Based on the above information, persons who are professionals in this field, it will be easy to understand that this invention can be widely applied. Numerous practical embodiments and adaptations of the present invention, in addition to those described in this application, as well as numerous variations, modifications and equivalent actions, will be obvious or reasonably clear on the basis of this invention and the above descriptions, without deviating from the essence and scope of this invention .

Accordingly, despite the fact that the invention was described in detail in this application in relation to one or more preferred embodiments, it should be understood that the information provided is for illustrative purposes only and is intended to give an idea of this invention and is provided solely for the purpose of providing complete and useful information. practical point of view of information about the invention. The above information should not be construed as limiting the invention or otherwise excluding any other embodiments, adaptations, variations, modifications or equivalent actions; this invention is limited only by the patent claims described in the appendix to this application and their equivalents.

Claims (21)

1. A method of creating functional images and non-invasive assessment of the distribution of electrical excitations in biological tissues, comprising stages in which:
first carry out the process of creating electromagnetic tomographic images to form a basic anatomical image of biological tissue;
then repeatedly:
conducting the process of creating electromagnetic tomographic images to form sequential images of biological tissue;
comparing each subsequent image with the previous image to determine the relative physiological changes in biological tissue; and
according to the result of the comparison, a differential image is formed that illustrates the magnitude of the relative physiological change in the biological tissue, and
at least one of the following differential images is combined indicating a relative physiological change with respect to the basic anatomical image of the biological tissue to be displayed as a single combined image;
the process of creating electromagnetic tomographic images contains:
provide many sources of electromagnetic fields for the formation of the electromagnetic field in a given area;
providing a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic field region in a given region;
place biological tissue in a given area;
form the region of the electromagnetic field through a selected set of sources of electromagnetic fields;
selectively determine the parameters of the electromagnetic field generated by each of the sources of the electromagnetic field so that each of the selected plurality of detectors of the electromagnetic field “recognizes” the source of the electromagnetic field from the plurality of sources of the electromagnetic field;
controlling the sources of the electromagnetic field and the detectors of the electromagnetic field so that the electromagnetic fields generated by the selected set of sources of the electromagnetic field are received by the selected set of detectors of the electromagnetic field after interacting with the biological tissue;
based on at least a portion of the electromagnetic field received by the detector, the characteristics of at least the electromagnetic field generated by the biological tissue are measured;
determining the image information of the biological tissue based on the measured interference parameters. 2. The method according to p. 1, which further comprises a preliminary step, which is input into the computer creating images, which controls the method, the length of time to perform repetitive operations of the process of creating electromagnetic tomographic images to form sequential images of biological tissue,
comparing each subsequent image with a previous image to determine a relatively physiological change in biological tissue; and
a difference image is formed from the comparison result, which illustrates the magnitude of the relative physiological change. 3. The method of claim 2, wherein the length of time is administered as a unit of time. 4. The method of claim 2, wherein the length of time is administered as the number of cycles of physiological activity. 5. The method according to p. 1, which further comprises a preliminary step, which is used to enter an image creation computer that controls the method, such as the image to be examined. 6. The method according to p. 5, in which the soft tissue of the extremities of the heart muscle or brain tissue is examined as biological tissue, the method being carried out as part of a dynamic study of the normal physiological activity of biological tissue. 7. The method according to claim 5, in which the myocardium or muscle tissue is examined as biological tissue, the method is carried out as part of a controlled stress study to assess the functional viability of biological tissue during exercise or other physiological stress. 8. The method according to claim 5, in which the myocardium or muscle tissue is examined as biological tissue, the method is carried out as part of a controlled stress study to assess the functional viability of biological tissue during pharmacologically induced stress. 9. The method of claim 1, further comprising the step of calculating system parameters by a computer that controls the method based on the length of time entered by the user, such as the image being examined, entered by the user, or both. 10. The method according to p. 9, in which these parameters include one or more of the required resolution time (time intervals between cycles of the process of creating electromagnetic tomographic images (frames)), the number of frames received by the reproducing computer, the required measurement accuracy in amplitude, required accuracy of phase measurements and the required accuracy of polarization measurements. 11. The method of claim 1, further comprising administering an electromagnetic contrast agent to the biological tissue. 12. The method according to p. 11, in which the contrast agent contains synthetic composite functional nanoparticles. 13. The method according to p. 1, in which at a repeating step in the process of creating electromagnetic tomographic images for the formation of sequential images of biological tissue using the latest image as a starting point in the formation of the subsequent image. 14. The method according to p. 1, in which the process of creating electromagnetic tomographic images further comprises a step, which carry out the correction step to minimize the effects of moving body tissue during the process. 15. The method according to claim 1, in which the basic anatomical image is represented in the form of dark and light gray tones and the relative physiological change is represented through various colors superimposed on the gray anatomical image. 16. The method of claim 1, wherein the relative physiological change is expressed as a percentage change. 17. The method of claim 16, wherein various colors are used to represent different percent change values. 18. A method of creating functional images and non-invasive assessment of the distribution of electrical excitations in biological tissues, comprising stages in which:
first carry out the process of creating electromagnetic tomographic images to form a basic anatomical image of biological tissue;
then repeatedly:
conducting the process of creating electromagnetic tomographic images to form successive images of biological tissue, with each subsequent image showing a relative physiological change in the biological tissue relative to the previous image of the biological tissue; and
at least one of the following differential images is combined indicating a relative physiological change with respect to the basic anatomical image of the biological tissue to be displayed as a single combined image;
the process of creating electromagnetic tomographic images contains:
provide many sources of electromagnetic fields for the formation of the electromagnetic field in a given area;
providing a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic field region in a given region;
place biological tissue in a given area;
form the region of the electromagnetic field through a selected set of sources of electromagnetic fields;
selectively determine the parameters of the electromagnetic field generated by each of the sources of the electromagnetic field so that each of the selected plurality of detectors of the electromagnetic field “recognizes” the source of the electromagnetic field from the plurality of sources of the electromagnetic field;
controlling the sources of the electromagnetic field and the detectors of the electromagnetic field so that the electromagnetic fields generated by the selected set of sources of the electromagnetic field are received by the selected set of detectors of the electromagnetic field after interacting with the biological tissue;
based on at least a portion of the electromagnetic field received by the detector, the characteristics of at least the electromagnetic field generated by the biological tissue are measured;
determining the image information of the biological tissue based on the measured interference parameters. 19. A method of creating functional images and non-invasive assessment of the distribution of electrical excitations in biological tissues, comprising stages in which:
first carry out the process of creating electromagnetic tomographic images to form a basic anatomical image of biological tissue;
then carry out the process of creating electromagnetic tomographic images to form a later image of biological tissue,
comparing the later image with the previous image to determine the relative magnitude of the physiological change in the areas across the biological tissue,
forming image information displaying the relative magnitude of the physiological change in the areas across the biological tissue, as determined in the comparison step,
combine the formed image with the basic anatomical image; and
displaying the result of the comparison step as a single combined image to represent the relative magnitude of the physiological change relative to the background baseline anatomical image;
the process of creating electromagnetic tomographic images contains:
provide many sources of electromagnetic fields for the formation of the electromagnetic field in a given area;
providing a plurality of electromagnetic field detectors for determining parameters of at least a portion of the electromagnetic field region in a given region;
place biological tissue in a given area;
form the region of the electromagnetic field through a selected set of sources of electromagnetic fields;
selectively determine the parameters of the electromagnetic field generated by each of the sources of the electromagnetic field so that each of the selected plurality of detectors of the electromagnetic field “recognizes” the source of the electromagnetic field from the plurality of sources of the electromagnetic field;
controlling the sources of the electromagnetic field and the detectors of the electromagnetic field so that the electromagnetic fields generated by the selected set of sources of the electromagnetic field are received by the selected set of detectors of the electromagnetic field after interacting with the biological tissue;
based on at least a portion of the electromagnetic field received by the detector, the characteristics of at least the electromagnetic field generated by the biological tissue are measured;
determining the image information of the biological tissue based on the measured interference parameters. 20. System (10) for creating functional images and non-invasive assessment of the distribution of electrical excitations in biological tissues, containing:
a plurality of sources (26) of an electromagnetic field for forming an area of an electromagnetic field in a given area;
a plurality of electromagnetic field detectors (28) for determining parameters of at least a portion of the electromagnetic field region in a given region;
a working chamber (12) for placing biological tissue (19) in a given area;
a controller (14) operatively connected to a plurality of electromagnetic field sources and electromagnetic field detectors for generating electromagnetic fields generated by a selected plurality of electromagnetic field sources and receiving signals by a selected plurality of electromagnetic field detectors after interaction of signals with biological tissue;
a module (30) for estimating the interference parameters of the electromagnetic field caused by at least the electromagnetic field generated by the biological tissue;
a computer (15) for creating images, creating the combined anatomical and physiological images of the biological tissue and the distribution of electrical excitation in the biological tissue by inverting the electromagnetic fields set by a plurality of electromagnetic field detectors; and
a display for graphically displaying the combined anatomical and physiological images of biological tissue, while the computer (15) for creating images contains working units (102, 104, 106, 108, 110, 112, 144) that extract information about the dynamic variable functional image and carry out dynamic combination of information about the anatomical image and the variable functional image. 21. A method for creating four-dimensional electromagnetic tomographic (EMT) dynamic combined images of biological tissues, comprising stages in which:
provide many sources (26) of electromagnetic field for the formation of the electromagnetic field in a given area;
providing a plurality of electromagnetic field detectors (28) for determining parameters of at least a portion of the electromagnetic field region in a given region;
place biological tissue (19) in a predetermined area;
form the region of the electromagnetic field through a selected set of sources of electromagnetic fields;
selectively determine the parameters of the electromagnetic field generated by each of the sources of the electromagnetic field so that each of the selected set of detectors of the electromagnetic field "recognizes" the source of the electromagnetic field from the set of sources of the electromagnetic field;
control the sources of the electromagnetic field and the detectors of the electromagnetic field so that the electromagnetic fields generated by the selected set of sources of the electromagnetic field are received by the selected set of detectors of the electromagnetic field after interacting with the biological tissue;
based on at least a portion of the electromagnetic field obtained by each electromagnetic field detector, the interference parameters of the electromagnetic field, at least the electromagnetic field generated by the biological tissue, are measured using at least a portion of the electromagnetic field data obtained by each of the electromagnetic field detectors;
while from the measured interference characteristics determine the information of the anatomical image and dynamically allocate time-varying information of the functional image, each of which relates to biological tissue;
dynamically mix the information of the anatomical image and the functional image for display by the display means.

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