Patent Application
20200163578
The present invention relates to a system for measuring the electrical impedance in human tissues, more in particular to a system for measuring the electrical impedance for the electrical discrimination and characterization of human tissues and even more in particular for the discrimination of cancer tissues.
In particular, it regards a system for electrical-impedance tomography of human tissue and for the discrimination of various types of human tissues.
Cancer diagnosis is currently based upon radiological/endoscopic imaging and nuclear imaging, for morphological and functional evaluation of lesions, respectively. However, it is well known that differential diagnosis of lesions may at times be critical on account of the unsatisfactory sensitivity and of the specificity of both of the analysis methods and of histological examination of tissue samples.
In particular, it is frequently difficult to distinguish tumours from inflammatory masses. More invasive and costly procedures, such as image-guided biopsies, may also be inconclusive as tissue sampling may not be adequately targeted. A useful instrument for improving precision of current methods is represented by quantitative evaluation of the electrical properties of tissues.
In fact, the various types of tissue have different conductivity parameters, and, assuming that the presence of a neoplastic tissue alters this structure, the differences in the electrical properties of normal tissue and cancer tissue may constitute useful information in clinical applications. Moreover, by displaying the structural homogeneity and providing impedance maps to identify and analyse the area of interest more precisely may be useful in many diagnostic applications or during endoscopic operations, with the aim of studying suspect tissues.
Electrical-impedance tomography (EIT) is a technique of reconstruction of the electrical image of the tissues, which may provide a 2D cross-sectional view of the body of a patient. EIT, as compared to other techniques, is less expensive, smaller, and safer because it does not require the use of radiation, strong magnetic fields, or injection of radioactive markers.
Electrical-impedance spectroscopy (EIS) is a method for measuring electrical impedance of a substance as a function of the applied frequency.
The value of the impedance and the dependence of impedance upon frequency are both dependent upon tissue composition. Measurement of the impedance of tissues within a range of frequencies generates a spectrum that is characteristic of biological tissue. Modifications of the impedance spectrum may hence be directly correlated to the changes in the underlying nature of the tissue.
The aim of the present invention is to provide a system for measuring electrical impedance in human tissues that can perform measurements with a high degree of accuracy and reliability.
Another aim is to provide a measurement system with an improved spatial resolution.
A further aim is to provide a measurement system that combines the EIT and EIS techniques.
According to the present invention, the above aims and others still are achieved by a system for measuring electrical impedance in human tissues comprising a plurality of needles; said plurality of needles being arranged along a circumference; where said plurality of needles have a length greater than 0.5 cm; said plurality of needles being coated with an electrically insulating material throughout their entire length except for a portion having a maximum length of 0.5 mm; each of said plurality of needles being connected to a multiplexer; an alternating-current generator being connected to an input of said multiplexer; where said current generator sends a current at at least two different frequencies ranging between 10 Hz and 1 MHz; a voltmeter being connected to an output of said multiplexer; a control centre connecting selectively and in succession said current generator to first two needles of said plurality of needles; said control centre controlling said multiplexer so as to connect selectively and in succession said voltmeter to second two needles of said plurality of needles according to a predefined scheme; said control centre measuring the impedance between said second two needles at said at least two frequencies; said control centre calculating an image, having a size substantially equal to that of said circumference, for each of said at least two frequencies corresponding to said measurement of the impedance between said second two needles; said control centre supplying said image to a system for displaying said image.
The above aims are moreover achieved by a method for measuring electrical impedance in human tissues comprising the steps of: applying a plurality of needles arranged along a circumference to a human tissue to reach a pre-set depth in said human tissue; supplying an alternating current, at at least two different frequencies in succession, selectively to one pair of needles, at a time, of said plurality of needles; measuring the impedance between all the other needles of said plurality of needles; and composing images, having a size substantially equal to that of said circumference, based upon the values of impedance measured.
Further characteristics of the invention are described in the dependent claims.
The advantages of the present solution over the solutions of the prior art are various.
The device developed is designed to explore the surface and the first layers of tissue. The central measurement core can be shifted to a lower level on the basis of the length of the needle.
The characteristics and advantages of the present invention will emerge clearly from the ensuing detailed description of a practical embodiment thereof, illustrated by way of non-limiting example in the annexed plate of drawings, wherein:
With reference to the attached FIGURE, a system for measuring electrical impedance in human tissues, according to the present invention, comprises eight electrodes 10 numbered 1 through 8. They are fixed in a plastic disk 11, having a thickness of approximately 0.5 cm, which keeps them parallel and all at the same height. The electrodes 10 pass through the disk 11, but are fixed thereto, and come out also at the back.
In the example of embodiment, eight electrodes are used, but a different number may be used, ranging, for example, between four and twelve.
The electrodes 10 are arranged along a circumference typically having a radius of 1.5 cm but in any case, preferably ranging between 0.5 and 5 cm.
The electrodes 10 are needles having a length of approximately 4 cm, of which approximately 2 cm exit from the disk 11 in the side defined as front and the remaining part of the needles in part is fixed in the disk 11 and in part exits from the back.
The needles have a diameter of approximately 0.3 mm and are made of stainless steel.
The length of the electrodes that comes out at the front from the disk 11 may vary according to the requirements and may be between 0.5 and 5 cm, according to the total length of the needle and the arrangement of the disk 11.
Each electrode 10 is entirely coated by an electrical insulator, for example polytetrafluoroethylene (PTFE), except for a portion at the tip 12 having a maximum length of 0.5 mm, typically 0.2 mm.
The electrodes 10 at the back are soldered to electric wires and are connected to one side of a multiplexer 15.
Connected on the other side of the multiplexer 15 is a current generator 20, which supplies a measurement current 21 in a selective way to pairs of electrodes 10.
The current generator 20 supplies an alternating current having a frequency ranging between 1 kHz and 1 MHz, more preferably between 10 kHz and 100 kHz.
The same measurement, applied to the same electrodes, is repeated for different frequencies in the aforesaid range so as to obtain a number of results at different frequencies.
Measurement of the impedance of the tissues varies as the frequency varies, and execution of a number of measurements (i.e., acquisition of a plurality of EIT images) enables a better evaluation of the alterations detected.
Connected again on the other side of the multiplexer 15 is a voltmeter 22, which reads the voltage 23 in a selective way from pairs of electrodes 10.
The current supplied is limited to 2 mA.
The multiplexer 15 may be physically made up of a number of multiplexers (for example, four) to be able to manage two inputs for the current generator and two outputs for the voltmeter and the eight electrodes.
The current generator 20, the voltmeter 22, and the multiplexer 15 are controlled by a control centre 25, typically a computer, a microcontroller, a tablet, or a smartphone, which are provided, inter alia, with a screen 26 for displaying the results of the measurements.
In the case where a portable device were to be provided, the communications between the various elements or between the computer and the device may be of a wireless type.
The control centre 25 is responsible for processing the data and reconstructing the impedance maps, for example, according to a protocol described in the paper by B. H. Brown and A. D. Seagar, “The Sheffield data collection system”, Clin. Phys. Physiol. Meas., vol. 8, pp. 91-97, 1987.
This protocol uses a single-source EIT (Electrical Impedance Tomography) system with N electrodes in a 2D circular plane and is based upon a protocol that simultaneously activates two electrodes for current stimulation and two electrodes for voltage acquisition.
It requires the electrodes N to be evenly distributed in one and the same plane. The number of configurations for reconstructing the impedance map is computed as N(N−3). Considering eight electrodes, a total of forty configurations are managed by the algorithm, i.e., forty impedance measurements for each frequency.
An alternating current at a first frequency is injected between a pair of adjacent electrodes, for example 1 and 2, and the measurements are performed, in sequence, between pairs of adjacent electrodes that do not carry current, namely, V4-V3, V5-V4, V6-V5, V7-V6 and V8-V7. The measurement is repeated one or more times, changing the frequency.
Then an alternating current at the first frequency is injected between the electrodes 2 and 3, and the measurement between V5-V4, V6-V5, V7-V6, V8-V7, and V1-V8 is made. The measurement is repeated one or more times, changing the frequency.
The measurements are repeated on all the pairs of electrodes so as to supply current to all the pairs of electrodes and carry out the measurements between all the other electrodes present.
The control centre records the measurements made and supplies 2D images of the area measured, i.e., images having a size substantially equal to that of the circumference along which the electrodes 10 are arranged.
The measurements made are complex measurements defined by a real part and an imaginary part or else by magnitude and phase. Hence, it is possible to obtain images representing values for each type of elements of the complex number.
The images are obtained by assigning, for example, different colours to different impedance values, or else by representing graphically the variations of impedance.
In particular, the images are obtained as described in what follows.
The data are saved to a text file in which for each row the real part, the imaginary part, and the magnitude of the impedance at the various frequencies are stored. Hence, the text file is an N×M array in which each row contains the measurements at a different frequency. N is, for example, equal to 10 (from 1 kHz to 10 kHz), whereas M is, for example, equal to 3 (one column for the real values, one for the imaginary values, and one for the magnitude).
The control centre builds in real time a graph with the values of the third column that correspond to the values of the magnitude of the impedance.
The real part (column 1) and the imaginary part (column 2) are then plugged into the following equation to compute the phase at the various frequencies
During reconstruction of the EIT images, the data gathered are arranged in an array of, for example, 40×10 (i.e., 40 measurements of impedance for 10 different frequency values), in which each TOW is the frequency scan of a particular configuration of electrodes following the Sheffield protocol.
Preferably, prior to the measurements on the tissue, fifty measurements are recorded in physiological solution. From the data obtained, the median is computed. The EIT image will then be reconstructed in a differential way between the data recorded from the tissue and the median of the physiological solution calculated.
The measurement system described envisages a real-time dual analysis of the tissues. Real-time response is very important in the diagnostic field as it makes it possible to have immediately information on the nature of the suspect lesion and hence act accordingly with analyses that are more problem-oriented.
Via the EIS analysis, as soon as the measurement starts, it is possible to show on the screen of a PC a graph that is characteristic of the structure of the tissue. The graph will show the frequency response (10 Hz to 10 kHz) of the impedance. The various graphs are stored in memory as long as the operator deems it appropriate to be able to compare the profiles obtained by positioning the probe in different points of the tissue, whether cancer tissue or healthy tissue. It will consequently be possible to evaluate the differences thereof and identify the correct range of characteristic values of the cancer tissue. The control centre will indicate to the operator whether it is cancer tissue or other tissue. The range of characteristic values of the cancer tissue will be established via the continuous collection of data in order to be able to create a database for the various types of cancer.
Via EIS analysis, the control centre will display on the screen images at various frequencies, which identify the variation of impedance in the tissue. In particular, according to the type of tissue enclosed in the measurement range of the probe (within the electrodes arranged in a circle), it will colour the cancer tissue and the healthy tissue or the tissue of some other nature differently.
Positioning of the electrodes is made by arranging them on the surface of the human tissue and/or inserting them into the tissue to the desired depth allowed by the length of the electrodes and their positioning in the disk 11.
It is possible to obtain images at a number of frequencies and at a number of depths thanks to the practically total insulation of the electrodes with just a few tenths of a millimetre exposed and conductive.
The present solution may be applied also in the case where four electrodes are used applying an alternating current, at at least two different frequencies in succession, to a pair of needles and measuring the impedance between a further two needles.
From experiments it emerges that it is possible to distinguish cancer tissues from healthy tissues, on the basis of the images obtained with the present invention, where significant variations of the impedance measured are found and in particular where reduction of impedance is found.
A possible application of the present invention is also that of coupling the system to a biopsy needle in order to improve sampling of the tissue, for example by positioning the biopsy needle at the centre of the electrodes.
Standard biopsy procedure is subject to certain problems due to current endoscopic and/or radiological procedures, which do not enable correct targeting of the biopsy during tissue sampling, it being frequently difficult to identify the cancer tissue without collecting a considerable number of samples. Moreover, biopsy is a complex procedure and is associated with collateral problems for the patient, requires long hospitalization, and cannot guarantee real-time diagnosis of the illness.
Via the use of in depth EIT images it is hence possible to position the probe in the proximity of the suspect mass and reconstruct the electrical heterogeneity of the tissue. The maps will return a mapping of the tissue according to the different structure recorded, thus identifying and differentiating the cancer areas from those of another nature. Under the guide of the reconstructed electrical image, it will thus be possible to sample the tissue in a more focused way, reducing the amount of tissue sampled and consequently the number of false positives and false negatives, and also reducing the invasiveness of the procedure and harm to the patient.
| Number | Date | Country | Kind |
|---|---|---|---|
| 102017000078157 | Jul 2017 | IT | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/IB2018/055058 | 7/10/2018 | WO | 00 |
