Patent Description:
Electric field therapy is a therapy implemented through a portable, non-invasive medical device, and its principle is to use a low-intensity, medium-frequency designed electric field to apply to such target biological tissue as microtubules having proliferation and diseased cells, interfere with the mitosis of diseased cells, and cause affected diseased cells to undergo apoptosis and inhibit the growth of the diseased cells.

Currently, in the existing devices used to destroy diseased cells or inhibit the division of diseased cells, an electrical signal generator applies a series of electrical signals to an electrode pair. Since two electrodes in the electrode pair are directly facing each other, a vertical electric field is generated between the two directly facing electrodes of the electrode pair, and the vertical electric field is applied to a target biological tissue region containing target biological tissue.

It has been found through research that a pair of electrodes is located at the periphery of a target biological tissue region, and target biological tissue (such as diseased cells) in the target biological tissue region is not guaranteed to be within the vertical electric field range of the pair of electrodes in the prior art, or is not located entirely within the vertical electric field range of the pair of electrodes in the prior art. That is, the coverage of the vertical electric field in the prior art is too fixed and small, so the coverage of the target biological tissue is limited, and thereby the intensity of the electric field covering a target biological tissue region is limited, and it is ineffective in inhibiting the division of such target biological tissue as diseased cells. <CIT> discloses a device for destroying and suppressing the rapid growth of diseased tissue in a patient.

In view of the shortcomings of the existing methods, the present application provides an electric field generating device, a control method for the electric field generating device, and a computer-readable storage medium, as defined in the appended set of claims, so as to solve the technical problem in the prior art that, it is ineffective in inhibiting the division of such target biological tissue as diseased cells due to the limited intensity of the electric field covering a target biological tissue region, and thereby the intensity of the electric field covering the target biological tissue is limited.

In the technical solution of the present application, n electrodes surround the target biological tissue region in a set manner, and the electrical signal generator is controlled to apply the first electrical signal to m electrodes of the n electrodes, and apply the second electrical signal to at least two electrodes of the n-m electrodes, where n is an integer not less than <NUM>, <NUM>≤m<n, and m is an integer. In the embodiments of the present application, it is able to flexibly select the quantity of electrodes surrounding the target biological tissue region according to a position of the target biological tissue in the target biological tissue region, and control which electrodes to be applied to the second electrical signal, so that a coverage area of the electric field generated between the electrodes with the first electrical signal and the electrodes with the second electrical signal best matches the position of the target biological tissue. Therefore, it is able to improve a matching degree between the coverage area of the electric field and the position of the target biological tissue, a coverage, and flexibility or adaptability of the electric field on the target biological tissue, thereby to increase the intensity of the electric field covering the target biological tissue, and further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

Moreover, multiple electric fields can be generated between the electrodes with the first electrical signal and at least two electrodes with the second electrical signal, and can be superimposed so as to enhance the intensity of an electric field at a superimposed region. When at least two electrodes with the second electrical signal are selected reasonably, it is able to improve the coverage of the electric field on the target biological tissue, thereby to improve the effect of inhibiting the division of such target biological tissue as diseased cells.

The additional aspects and advantages of the present disclosure will be given or may become apparent in the following description, or may be understood through the implementation of the present application.

The above and/or additional aspects as well as advantages of the present application will become apparent and are easily understood in the following description with reference to the following drawings. In these drawings,.

The present application provides an electric field generating device, a control method for the electric field generating device and a computer-readable storage medium, so as to solve the technical problem in the prior art that, it is ineffective in inhibiting the division of such target biological tissue as diseased cells due to the limited intensity of the electric field covering a target biological tissue region, and thereby the intensity of the electric field covering the target biological tissue is limited.

The present application will be described hereinafter in conjunction with the embodiments and the drawings. Identical or similar reference numbers in the drawings represent an identical or similar element or elements having an identical or similar function. In addition, the detailed description about any known technology will be omitted when it is unnecessary to the features in the present application. The following embodiments are for illustrative purposes only, but shall not be used to limit the scope of the present application as defined by the appended claims.

As can be appreciated by a person skilled in the art, unless otherwise defined, all terms (including technical and scientific terms) used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the present application is a part. Terms, such as those defined in commonly used dictionaries, should be interpreted as having a meaning that is consistent with their meaning in the context of the relevant art and will not be interpreted in an idealized or overly formal sense, unless expressly so defined herein.

In the case that one element is connected or coupled to another element, it may be directly connected or coupled to the other element, or an intermediate element may be arranged therebetween. At this time, the element may be connected or coupled to the other element in a wireless or wired manner. In addition, the expression "and/or" is used to indicate the existence of all or any one of one or more of listed items, or combinations thereof.

It has been found through research that a pair of electrodes is located at the periphery of a target biological tissue region, and target biological tissue (such as diseased cells) in the target biological tissue region is not guaranteed to be within the vertical electric field range of the pair of electrodes in the prior art, or is not located entirely within the vertical electric field range of the pair of electrodes in the prior art. That is, the coverage of the vertical electric field in the prior art is too fixed and small, so the coverage of the target biological tissue is limited, and thereby the intensity of the electric field covering a target biological tissue region is limited, and it is ineffective in inhibiting the division of such target biological tissue as diseased cells.

The present application provides a target electric field generating device and a control method for the electric field generating device, so as to solve the above technical problems in the prior art.

The technical solution of the present application and how to solve the above technical problems by using the technical solution of the present application will be described in detail hereinafter in conjunction with specific embodiments. The following specific embodiments can be combined with each other, and same or similar concepts or processes may not be reiterated in some embodiments. The embodiments of the present application will be described hereinafter with reference to the accompanying drawings.

The electric field generating device in the embodiments of the present application is for surgical use and is applicable for surgical medical instruments.

The present application provides a target electric field generating device, as shown in <FIG>, the electric field generating device includes n electrodes <NUM>, an electrical signal generator <NUM> and a control signal generator <NUM>. In specific, n electrodes <NUM> are configured to surround a target biological tissue region in a set manner; where n is an integer not less than <NUM>. The target biological tissue region includes the target biological tissue and a normal biological tissue, and the target biological tissue includes diseased cells, a tumor or a lesion, etc. The lesion refers to a diseased part of a body, or a localized and diseased tissue in the body that contains pathogenic microorganisms. For example, if a certain part of a lung is destroyed by tuberculosis bacteria, this part is a tuberculosis lesion. The normal biological tissue refers to a biological tissue that does not contain diseased cells, a tumor and a lesion, and can be considered as a biological tissue other than the target biological tissue.

The electrical signal generator <NUM> is electrically connected to the n electrodes <NUM>.

The control signal generator <NUM> is electrically connected to the electrical signal generator <NUM>, and configured to control the electrical signal generator <NUM> to apply a first electrical signal to m electrodes of the n electrodes <NUM>, and apply a second electrical signal to at least two electrodes of n-m electrodes, to generate an electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal, where a voltage of the second electrical signal is less than a voltage of the first electrical signal, <NUM>≤m<n, and m is an integer.

Optionally, the first electrical signal and the second electrical signal may be outputted by one electrical signal generator, or may be outputted by two electrical signal generators respectively.

Optionally, the n electrodes <NUM> may be attached to a target part of a human body or an animal body according to the set manner.

Optionally, there is at least one electrode with the first electrical signal and at least two electrodes with the second electrical signal. According to the claimed invention, the quantity of electrodes with the first electrical signal is smaller than the quantity of electrodes with the second electrical signal.

Optionally, the control signal generator <NUM> may be a central processing unit (Central Processing Unit, CPU), a general-purpose processor, a data signal processor (Digital Signal Processor, DSP), an application specific integrated circuit (Application Specific Integrated Circuit, ASIC), or a field-programmable gate array (Field-Programmable Gate Array, FPGA) or other programmable logic devices, transistor logic devices, hardware members or any combination thereof. It may implement or execute various illustrative logical blocks, modules and circuits described in connection with the content of the present application. The control signal generator <NUM> may also be a combination that implements computing functions, such as a combination of one or more microprocessors, a combination of a DSP and a microprocessor, etc..

In the embodiments of the present application, it is able to flexibly select the quantity of electrodes surrounding the target biological tissue region according to a position of the target biological tissue in the target biological tissue region, and control which electrodes to be applied to the second electrical signal, so that a coverage area of the electric field generated between the electrode with the first electrical signal and the electrodes with the second electrical signal best matches the position of the target biological tissue. Therefore, it is able to improve a matching degree between the coverage area of the electric field and the position of the target biological tissue, a coverage, and flexibility or adaptability of the electric field on the target biological tissue, thereby to increase the intensity of the electric field covering the target biological tissue, and further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

Moreover, multiple electric fields can be generated between the electrode with the first electrical signal and at least two electrodes with the second electrical signal, and can be superimposed so as to enhance the intensity of an electric field at a superimposed region. When at least two electrodes with the second electrical signal are selected reasonably, it is able to improve the coverage of the electric field on the target biological tissue, thereby to improve the effect of inhibiting the division of such target biological tissue as diseased cells.

In some embodiments, as shown in <FIG>, the electrical signal generator <NUM> includes a first electrical signal generating circuit <NUM> and a second electrical signal generating circuit <NUM>. The first electrical signal generating circuit <NUM> is electrically connected to the n electrodes, and configured to output the first electrical signal. The second electrical signal generating circuit <NUM> is electrically connected to the n electrodes and configured to output the second electrical signal.

In some embodiments, as shown in <FIG>, the electric field generating device further includes a first switch assembly <NUM> and a second switch assembly <NUM>. The first electrical signal generating circuit <NUM> is electrically connected to the n electrodes <NUM> through the first switch assembly <NUM>, and the control signal generator <NUM> is electrically connected to the first switch assembly <NUM>. The second electrical signal generating circuit <NUM> is electrically connected to the n electrodes <NUM> through the second switch assembly <NUM>, and the control signal generator <NUM> is electrically connected to the second switch assembly <NUM>. The control signal generator <NUM> is configured to control the first switch assembly <NUM> to transmit the first electrical signal to m electrodes of the n electrodes <NUM>, and control the second switch assembly <NUM> to transmit the second electrical signal to at least two electrodes of n-m electrodes, to generate the electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal.

In some embodiments, as shown in <FIG>, the first switch assembly <NUM> includes n first switch units <NUM>, and the second switch assembly <NUM> includes n second switch units <NUM>. The n first switch units <NUM> are electrically connected to the n electrodes <NUM> respectively, and electrically connected to the first electrical signal generating circuit <NUM> and the control signal generator <NUM>. The n second switch units <NUM> are electrically connected to the n electrodes <NUM> respectively, and electrically connected to the second electrical signal generating circuit <NUM> and the control signal generator <NUM>.

Optionally, the n first switch units include a first one of the first switch units to an nth one of the first switch units, the n second switch units include a first one of the second switch units to an nth one of the second switch units, and the n electrodes include a first electrode to an nth electrode.

The first one to the nth one of the first switch units and the first one to the nth one of the second switch units are electrically connected to n electrodes respectively, i.e., the first one of the first switch units and the first one of the second switch units are electrically connected to the first electrode, a second one of the first switch units and a second one of the second switch units are electrically connected to the second electrode,. , the nth one of the first switch units and the nth one of the second switch units are electrically connected to the nth electrode.

Optionally, as shown in <FIG>, the electric field generating device further includes a multi-channel analog switch unit <NUM> electrically connected to n first switch units <NUM>, n second switch units <NUM>, and the control signal generator <NUM> and configured to control switching of the transmission path of the control signal outputted by the control signal generator <NUM>. The multi-channel analog switch unit <NUM> has such advantages as fast switching speed, no jitter, low power consumption, small size, reliable operation and being easy to be controlled.

In some embodiments, the electric field generating device further includes at least one of the following:.

The constant voltage signal means that a size of the voltage is maintained, the fluctuating voltage signal means that the sum of absolute values of positive and negative deviations of the voltage does not exceed <NUM>% of a rated value.

Optionally, the first electrical signal generating circuit <NUM> includes an alternating current signal generating circuit, a pulse electrical signal generating circuit or a square wave electrical signal generating circuit, the alternating current signal generating circuit is used to output an AC voltage signal, the pulse electrical signal generating circuit is used to output a pulse voltage signal, and the square wave electrical signal generating circuit is used to output a square wave voltage signal.

In some embodiments, the absolute value of the voltage amplitude of the second electrical signal is 0V, 1V or 5V.

As shown in <FIG>, n=<NUM> is set for illustrative purposes only. As can be appreciated, n may also be any other quantities, such as <NUM>, <NUM>, <NUM>, which is not particularly defined in the present application. The electric field generating device is used to apply an electric field to a target biological tissue region <NUM>, the target biological tissue region <NUM> may be a target region of a patient. In <FIG>, there are six electrodes (electrode <NUM>, electrode <NUM>, electrode <NUM>, electrode <NUM>, electrode <NUM> and electrode <NUM>) surrounding the target biological tissue region <NUM> (e.g., the electrodes <NUM>-<NUM> may be arranged to be in contact with the patient's body).

Specifically, the first electrical signal generating circuit <NUM> is electrically connected to six electrodes and used to apply the first electrical signal to the six electrodes. The second electrical signal generating circuit <NUM> is electrically connected to the six electrodes and used to apply the second electrical signal to the six electrodes.

Optionally, the control signal generator <NUM> controls one of the first switch units <NUM> to transmit the first electrical signal to the electrode <NUM>, and controls the remaining first switch units <NUM> to be turned off. At the same time, the control signal generator <NUM> controls one of second switch units <NUM> that is electrically connected to the electrode <NUM> to be turned off, and controls the remaining second switch units <NUM> to transmit the second electrical signal to the electrodes <NUM>-<NUM>.

For example, the electrode <NUM> is controlled to have the first electrical signal, and the electrodes <NUM>-<NUM> are controlled to have the second electrical signal, so a first electric field is generated between the electrode <NUM> and the electrode <NUM>, a second electric field is generated between the electrode <NUM> and the electrode <NUM>, a third electric field is generated between the electrode <NUM> and the electrode <NUM>, a fourth electric field is generated between the electrode <NUM> and the electrode <NUM>, and a fifth electric field is generated between the electrode <NUM> and the electrode <NUM>. The first electrical signal applied to the electrode <NUM> is controlled to be a high voltage signal (for example, between <NUM> and 500V), and the second electrical signal applied to the electrodes <NUM>-<NUM> is controlled to be a low voltage signal (for example, <NUM> to 10V), that is, there are multiple potential differences between the electrode <NUM> and the electrodes <NUM>-<NUM>, and multiple electric fields are generated between the electrodes <NUM> and the electrodes <NUM>-<NUM>, so it is able to increase the coverage area of the electric field on the patient's target region, and thereby increase the intensity of the electric field covering the patient's target region, increase the intensity of the electric field covering the target biological tissue, where the target biological tissue region includes the target biological tissue and the normal biological tissue, and improve the effect of inhibiting the division of such target biological tissue as diseased cells.

As can be appreciated, it is able to control the electrode <NUM> and the electrode <NUM> to have the first electrical signal, and the electrodes <NUM>-<NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM> and the electrode <NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM>, the electrode <NUM> and the electrode <NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM>, the electrode <NUM> and the electrode <NUM> to have the second electrical signal, which is not particularly defined in the present application.

Optionally, still referring to <FIG>, one of the first switch units <NUM> is controlled to transmit the first electrical signal to the electrode <NUM>, and the remaining first switch units <NUM> are controlled to be turned off. At the same time, one of the second switch units <NUM> that is electrically connected to the electrode <NUM> is controlled to be turned off, and the remaining second switch units <NUM> are synchronously controlled to be turned on sequentially according to a set order, so as to transmit the second electrical signal sequentially to the electrodes <NUM>-<NUM> according to the set order. That is, the electrode <NUM> is applied with the first electrical signal continuously, and the electrodes <NUM>-<NUM> are applied with the second electrical signal sequentially according to the set order (that is, the second electrical signal is switched among the electrodes <NUM>-<NUM> according to the set order).

Optionally, the set order includes: a clockwise order, a counterclockwise order, an n-pointed star shape order, or any other hop or non-continuous orders.

Optionally, a time interval for the second switch units <NUM> to be turned on or off sequentially according to the set order is not less than <NUM> and not greater than <NUM>.

Optionally, the electrode <NUM> is controlled to be applied with the first electrical signal within a first time period, the electrode <NUM> is controlled to be applied with the second electrical signal within a second time period, the electrode <NUM> is controlled to be applied with the second electrical signal within a third time period, the electrode <NUM> is controlled to be applied with the second electrical signal within a fourth time period, the electrode <NUM> is controlled to be applied with the second electrical signal within the fifth time period, and the electrode <NUM> is controlled to be applied with the second electrical signal within the sixth time period. The first time period, the second time period, the third time period, the fourth time period, the fifth time period and the sixth time period may be all the same, all different, or partially the same, and may be set according to actual situations, which is not particularly defined in the present application.

In the above-mentioned embodiment, the electrode <NUM> is controlled to be applied with the first electrical signal continuously, and the remaining electrodes <NUM>-<NUM> are controlled to be applied with the second electrical signal sequentially according to the set order, where the voltage of the second electrical signal applied to the remaining electrodes <NUM>-<NUM> is smaller than the voltage of the first electrical signal. As compared with applying the first electrical signal to all electrodes and switching the first electrical signal among all electrodes, in the embodiment of the present application, one electrode is applied with the first electrical signal, the remaining electrodes are applied with the second electrical signal, and the second electrical signal is switched among the remaining electrodes, so the power consumption is reduced, thereby reducing the power consumption of the electric field generating device and extending the standby duration of the battery used for power supply of the electric field generating device.

The electric field generated by the electric field generating device is used to destroy diseased cells or inhibit the division of diseased cells, and the electric field is referred as a tumor treating field (Tumor Treating Field, TTF) in the present application. TTF can inhibit the proliferation of rapidly dividing active cells, such as cancer cells, and disrupt these active cells.

Optionally, still referring to <FIG>, in order to prevent the electric field generating device from overheating, six first switch units <NUM> are controlled to be turned on sequentially according to the set order, so as to transmit the first electrical signal to the corresponding electrodes sequentially according to the set order. Six second switch units <NUM> electrically connected to the corresponding electrodes are synchronously controlled to be turned off sequentially according to the set order, and second switch units <NUM> that are not turned off are synchronously controlled to be turned on sequentially according to the set order, so as to transmit the second electrical signal to electrodes that do not receive the first electrical signal sequentially according to the set order.

Optionally, the time at which each electrode has the first electrical signal or the second electrical signal may be set according to actual situations, which is not particularly defined in the present application.

Thus, the electrodes <NUM>-<NUM> are applied with the first electrical signal and the second electrical signal sequentially according to the set order, which further reduces the power consumption of the electric field generating device, thereby preventing the electric field generating device from overheating.

Based on the same inventive concept, the present application provides in some embodiments a control method for the above-mentioned electric field generating device, including:.

In the control method for the electric field generating device of the embodiments of the present application, n electrodes surround the target biological tissue region in a set manner, and the electrical signal generator is controlled to apply the first electrical signal to m electrodes of the n electrodes, and apply the second electrical signal to at least two electrodes of the n-m electrodes, where n is an integer not less than <NUM>, <NUM>≤m<n, and m is an integer. In the embodiments of the present application, it is able to flexibly select the quantity of electrodes surrounding the target biological tissue region according to a position of the target biological tissue in the target biological tissue region, and control which electrodes to be applied to the second electrical signal, so that a coverage area of the electric field generated between the electrode with the first electrical signal and the electrodes with the second electrical signal best matches the position of the target biological tissue. Therefore, it is able to improve a matching degree between the coverage area of the electric field and the position of the target biological tissue, a coverage, and flexibility or adaptability of the electric field on the target biological tissue, thereby to increase the intensity of the electric field covering the target biological tissue, and further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

In addition, multiple electric fields can be generated between the electrode with the first electrical signal and at least two electrodes with the second electrical signal, and can be superimposed so as to enhance the intensity of an electric field at a superimposed region. When at least two electrodes with the second electrical signal are selected reasonably, it is able to improve the coverage of the electric field on the target biological tissue, thereby to improve the effect of inhibiting the division of such target biological tissue as diseased cells.

In some embodiments, controlling the electrical signal generator to apply the first electrical signal to m electrodes of the n electrodes, and apply the second electrical signal to at least two electrodes of the n-m electrodes, to generate the electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal includes:.

In some embodiments, controlling the first switch assembly to transmit the first electrical signal to m electrodes of the n electrodes, and controlling the second switch assembly to transmit the second electrical signal to at least two electrodes of the n-m electrodes, to generate the electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal includes:
controlling a first one of first switch units to transmit the first electrical signal to a first electrode of n electrodes, and controlling a second one of the first switch units to a nth one of the first switch units to be turned off; simultaneously controlling a first one of second switch units that is electrically connected to the first electrode to be turned off, and controlling at least two second switch units among a second one of the second switch units to an nth one of the second switch units to transmit the second electrical signal to at least two electrodes of n electrodes except the first electrode.

The first switch assembly includes n first switch units, and the second switch assembly includes n second switch units. The n first switch units include the first one of the first switch units to the nth one of the first switch units, the n second switch units include the first one of the second switch units to the nth one of the second switch units, and the n electrodes include the first electrode to an nth electrode.

As shown in <FIG>, n=<NUM> is set for illustrative purposes only. As can be appreciated, n may also be any other quantities, such as <NUM>, <NUM>, <NUM>, which is not particularly defined in the present application. The electric field generating device is used to apply an electric field to a target biological tissue region <NUM>, the target biological tissue region <NUM> may be a target region of a patient. In <FIG>, there are six electrodes (electrode <NUM>, electrode <NUM>, electrode <NUM>, electrode <NUM>, electrode <NUM> and electrode <NUM>) surrounding the target biological tissue region <NUM> (e.g., the electrodes <NUM>-<NUM> may be arranged to be in contact with the patient's body). In <FIG>, there are six first switch units <NUM>, namely, a first one to a sixth one of the first switch units. There are six second switch units <NUM> in <FIG>, namely, a first one to a sixth one of the second switch units.

For example, the electrode <NUM> is controlled to have the first electrical signal, and the control electrodes <NUM>-<NUM> are controlled to have the second electrical signal, so a first electric field is generated between the electrode <NUM> and the electrode <NUM>, a second electric field is generated between the electrode <NUM> and the electrode <NUM>, a third electric field is generated between the electrode <NUM> and the electrode <NUM>, a fourth electric field is generated between the electrode <NUM> and the electrode <NUM>, and a fifth electric field is generated between the electrode <NUM> and the electrode <NUM>.

The first electrical signal applied to the electrode <NUM> is controlled to be a high voltage signal (for example, between <NUM> and 500V), and the second electrical signal applied to the electrodes <NUM>-<NUM> is controlled to be a low voltage signal (for example, <NUM> to 10V), that is, there are multiple potential differences between the electrode <NUM> and the electrodes <NUM>-<NUM>, multiple electric fields are generated between the electrodes <NUM> and the electrodes <NUM>-<NUM>, and multiple electric fields can be superimposed so as to enhance the intensity of an electric field at a superimposed region. When at least two electrodes with the second electrical signal are selected reasonably, it is able to improve the coverage of the electric field on the target biological tissue, thereby to improve the effect of inhibiting the division of such target biological tissue as diseased cells.

As can be appreciated, it is also able to control the electrode <NUM> and the electrode <NUM> to have the first electrical signal, and the electrodes <NUM>-<NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM> and the electrode <NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM>, the electrode <NUM> and the electrode <NUM> to have the second electrical signal, or control the electrode <NUM> to have the first electrical signal, and the electrode <NUM>, the electrode <NUM> and the electrode <NUM> to have the second electrical signal, which is not particularly defined in the present application.

In some embodiments, controlling the first switch assembly to transmit the first electrical signal to m electrodes of the n electrodes, and controlling the second switch assembly to transmit the second electrical signal to at least two electrodes of the n-m electrodes, to generate the electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal includes:
controlling a first one of first switch units to transmit the first electrical signal to a first electrode of n electrodes, and controlling a second one of the first switch units to an nth one of the first switch units to be turned off; simultaneously controlling a first one of second switch units that is electrically connected to the first electrode to be turned off, and synchronously controlling at least two second switch units among a second one of the second switch units to an nth one of the second switch units to be turned on sequentially according to a set order, to transmit the second electrical signal to at least two electrodes of n electrodes except the first electrode according to the set order.

In the above-mentioned embodiment, one of n electrodes is controlled to be applied with the first electrical signal continuously, and the remaining electrodes <NUM>-<NUM> are controlled to be applied with the second electrical signal sequentially according to the set order, where the voltage of the second electrical signal applied to the remaining electrodes <NUM>-<NUM> is smaller than the voltage of the first electrical signal. As compared with applying the first electrical signal to all electrodes and switching the first electrical signal among all electrodes, in the embodiment of the present application, one electrode is applied with the first electrical signal, the remaining electrodes are applied with the second electrical signal, and the second electrical signal is switched among the remaining electrodes, so the power consumption is reduced, thereby reducing the power consumption of the electric field generating device.

By way of example, still referring to <FIG>, one of the first switch units <NUM> is controlled to transmit the first electrical signal to the electrode <NUM>, and the remaining first switch units <NUM> are controlled to be turned off. At the same time, one of the second switch units <NUM> that is electrically connected to the electrode <NUM> is controlled to be turned off, and the remaining second switch units <NUM> are synchronously controlled to be turned on sequentially according to the set order, so as to transmit the second electrical signal sequentially to the electrodes <NUM>-<NUM> according to the set order. That is, the electrode <NUM> is applied with the first electrical signal continuously, and the electrodes <NUM>-<NUM> are applied with the second electrical signal sequentially according to the set order (that is, the second electrical signal is switched among the electrodes <NUM>-<NUM> according to the set order).

In some embodiments, m is <NUM>, and controlling the first switch assembly to transmit the first electrical signal to m electrodes of the n electrodes, and controlling the second switch assembly to transmit the second electrical signal to at least two electrodes of the n-m electrodes, to generate the electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal includes:
controlling n first switch units to be turned on sequentially according to a set order, to enable n electrodes to receive the first electrical signal sequentially according to the set order, synchronously controlling n second switch units to be turned off sequentially according to the set order, and synchronously controlling second switch units combinations to be turned on sequentially according to the set order, to enable electrode combinations corresponding to the second switch units combinations to receive the second electrical signal sequentially according to the set order; where each second switch units combination includes at least two second switch units of n-<NUM> second switch units that are not turned off, each electrode combination includes at least two electrodes that do not receive the first electrical signal.

The first switch assembly includes the n first switch units, and the second switch assembly includes the n second switch units.

In the above-mentioned embodiment, n electrodes are controlled to have the first electrical signal (high voltage signal) and the second electrical signal (low voltage signal) sequentially according to the set order, which further reduces the power consumption of the electric field generating device, thereby preventing the electric field generating device from overheating.

Note that the target biological tissue region includes the target biological tissue and a normal biological tissue, and the target biological tissue includes diseased cells, a tumor or a lesion, etc..

In order to further verify the technical effect of the present application, a case where the target biological tissue is a tumor is taken as an example, a two-dimensional model is performed on the target biological tissue and n electrodes surrounding the target biological tissue region, and a three-dimensional model is performed on a human thorax and a tumor in the human thorax.

A finite element modeling process is as follows.

A geometric model is constructed in COMSOL. Next, a circle with a diameter of <NUM> (millimeters) is constructed as the tumor (i.e., the target biological tissue <NUM>), a square with a side length of <NUM> is constructed as the target biological tissue region <NUM>, where a center of the square coincides with a center of the circle of the tumor, and a region of the square outside the circle represents the normal biological tissue <NUM> outside of the tumor. Straight lines with a length of <NUM> (h1 is <NUM> in <FIG>) are arranged respectively in the middle of the four edges of the above square as electrodes. The constructed model is shown in <FIG>, and four electrodes are denoted as electrode <NUM>, electrode <NUM>, electrode <NUM> and electrode <NUM>.

Material electrical parameter settings. The conductivity of a tumor region (i.e., the target biological tissue <NUM>) is set to <NUM>/m and the dielectric constant thereof is set to <NUM>. The conductivity of a surrounding normal biological tissue <NUM> is set to <NUM>/m and the dielectric constant thereof is set to <NUM>.

Applied voltage waveform. In this embodiment, a continuous sine wave with a frequency of <NUM> (kilohertz) and a peak-to-peak value of 120V (volts) is applied, that is, the first electrical signal generating circuit is an AC signal generating circuit and outputs an AC voltage signal with a frequency of <NUM> (kilohertz) and a peak-to-peak value of 120V (volts).

Note that the first electrical signal outputted by the first electrical signal generating circuit is a high voltage signal, and the second electrical signal outputted by the second electrical signal generating circuit is a low voltage signal.

The electrode <NUM> is set as a power source receiving end, and configured to receive the first electrical signal outputted by the first electrical signal generating circuit, and the electrodes <NUM> to <NUM> are set as ground ends, and configured to receive the second electrical signal outputted by the second electrical signal generating circuit.

According to the above settings, following three cases are shown.

<FIG> shows the case where two electrodes are grounded. After calculation, an average field strength in the tumor region is <NUM>. As compared with the case where the single electrode is grounded, the average field strength in the tumor region is increased by <NUM>%.

Average field strengths on the tumor in different cases are shown in Table <NUM>.

Based on the above, when the quantity of electrodes with the high-voltage signal is maintained, the greater the quantity of electrodes with the low-voltage signal, the greater the average field strength in the tumor region.

In the embodiments of the present application, it is able to increase the coverage area of the electric field on the target biological tissue, increase the intensity of the electric field covering the target biological tissue region, and thereby increase the intensity of the electric field covering the target biological tissue, and improve the effect of inhibiting the division of such target biological tissue as diseased cells.

Construction of a human thorax. Approximate shapes of actual tissues are constructed in Rhino3D NURBS <NUM>, and compared with multiple (Computed Tomography, CT) scanning, slices, so as to modify boundary contours, thereby ultimately restoring a realistic human body model. The modeling content includes skin, fat, muscles, bones, lungs, heart and liver. Some over-detailed tissues (such as connective tissues, pleurae) that have similar electrical parameters and are difficult to model are merged into muscle tissues. A final model is shown in <FIG>.

Construction of a single electrode. Each electrode is modeled as a double-layer structure as shown in <FIG> (i.e., a first layer <NUM> and a second layer <NUM> in <FIG>), in which a layer having a large area (the first layer <NUM> in <FIG>) that is close to a skin is a gel layer with a diameter of <NUM> and a thickness ranging from <NUM> to <NUM>, a layer having a small area (the second layer <NUM> in <FIG>) is an insulation layer with a diameter of <NUM> and a thickness of <NUM>. The insulation layer is made of a ceramic material with high dielectric constant. The dielectric constant is close to <NUM>,<NUM>. The electric field is transmitted to the human body through the ceramic layer and gel layer.

Construction of an electrode array. The electrode array is composed of multiple electrodes. For example, <NUM> electrodes, <NUM> electrodes, <NUM> electrodes, and other quantities of electrodes may form multiple different electrode arrays. <FIG> and <FIG> show the distribution of the electrode arrays applicable for human thoracic lung cancer treatment, where <FIG> shows the layout of an initial electrode array.

As shown in <FIG>, electrode arrays applicable for lung cancer treatment are categorized into three types, namely, a front electrode array (a first electrode array <NUM> located on the front side of the thorax of a human body in <FIG>), a back electrode array (a first electrode array <NUM> located on the back of the human body in <FIG>) and a side electrode array (a third electrode array <NUM> located on one side of the human body in <FIG>). Due to the large skin area on the front side of the thorax and the back of the human body, the front electrode array and the back electrode array each include more electrodes, for example, the front electrode array (i.e., the first electrode array <NUM>) and the back electrode array (i.e., the second electrode array <NUM>) each include <NUM> electrodes. Due to limited placement space on both sides of the human body, the electrode arrays positioned laterally each include fewer electrodes. Specifically, the third electrode array <NUM> including <NUM> electrodes is placed on each side of the human body. As shown in <FIG>, the first electrode array <NUM> is arranged on the front side of the thorax of the human body, the second electrode array <NUM> is arranged on the back of the human body, the third electrode array <NUM> is arranged on a left side of the human body, and the third electrode array <NUM> is arranged on a right side of the human body. That is, four electrode arrays (i.e., the first electrode array <NUM>, the second electrode array <NUM>, the third electrode array <NUM> and the third electrode array <NUM>) are arranged on the front side of the thorax, back, left side, and right side of the human body.

Construction of Tumor Models. A total of four virtual tumor models are created, as shown in <FIG>, <FIG>. In these figures, the target biological tissues <NUM> are assumed as Tumors T1, T2, T3, and T4. The sizes and locations of four tumors are indicated by dashed circles in <FIG>, <FIG>. In <FIG>, Tumor T1 in a middle lobe of a right lung has a diameter of <NUM>. In <FIG>, Tumor T2 is in a middle lobe of the right lung. In <FIG>, Tumor T3 is in a middle lobe of a left lung. In <FIG>, Tumor T4 is in a lower lobe of a left lung. Tumors T2, T3 and T4 each have a diameter of <NUM>.

After the model has been constructed, separate meshes for various tissues including electrodes, gels, skin, fat, bones, muscles, lungs, heart, liver and tumors are generated through mesh generation by using HyperMesh14. <NUM>, and then imported into COMSOL Multiphysics <NUM> one by one, so as to solve electrical quasi-static equations of Maxwell's equations by using a current module.

Material electrical parameter settings. As shown in Table <NUM>, the conductivity and dielectric constant of each tissue are set to corresponding values.

Simulation power source settings: Frequency domain simulation is used, a frequency thereof is set to <NUM>, and a normal current density on each electrode is set to 100mA/cm<NUM> (milliamps per square centimeter).

Field strength evaluation method: COMSOL is used to calculate a curve diagram between the electric field strength-volume (EVH) at the tumor, as shown in <FIG>, where a horizontal axis is the field strength (V/cm), and a vertical axis is a volume ratio of the tumor (%). Each point on the curve represents a volume ratio of the tumor that is greater than a field strength value corresponding to the point. An area below the entire curve is used to represent the field strength coverage on the tumor, and the area can be obtained by integrating the curve. A value of the area is referred to as EAUC (Electric Field Area Under Curve).

The front electrode array is set as a power source receiving end, and configured to receive the first electric signal outputted by the first signal generation circuit, and the back electrode array, the left side electrode array and the right side electrode array are set as ground ends, and configured to receive the second electric signal outputted by the second signal generation circuit.

In the case of Tumor T1 and Tumor T2, simulation results are shown in Table <NUM>, where EAUC values are compared. Two cases presented in Table <NUM> are as follows.

As the results in Table <NUM> indicate, the EAUC value in the case where two electrode arrays are grounded is higher than the EAUC value in the case where the single electrode array is grounded, i.e., the EAUC value is increased. It can be observed from Table <NUM> that, for Tumor T1, the EAUC value in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded, is increased by <NUM>%. For Tumor T2, the EAUC value in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded, is increased by <NUM>%.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T1 is shown in <FIG> and <FIG>, where a position of Tumor T1 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the left side of the human body in <FIG> (e.g., a left part of <FIG>) is higher as compared with that on the left side of the human body in <FIG>.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T2 is shown in <FIG>, where a position of Tumor T2 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the left side of the human body in <FIG> (e.g., a left part in the figure) is higher as compared with that on the left side in <FIG>.

In the case of Tumor T3 and Tumor T4, simulation results are shown in Table <NUM>, where EAUC values are compared. Two cases presented in Table <NUM> are as follows.

As shown in Table <NUM>, the EAUC value in the case where two electrode arrays are grounded is higher than the EAUC value in the case where the single electrode array is grounded, i.e., the EAUC value is increased. It can be observed from Table <NUM> that, for Tumor T3, the EAUC value in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded, is increased by <NUM>%. For Tumor T4, the EAUC value in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded, is increased by <NUM>%.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T3 is shown in <FIG> and <FIG>, where a position of Tumor T3 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the right side of the human body in <FIG> (e.g., a right part in the figure) is higher as compared with that on the right side of the human body in <FIG>.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T4 is shown in <FIG>, where a position of Tumor T4 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the right side of the human body in <FIG> (e.g., a right part in the figure) is higher as compared with that on the right side of the human body in <FIG>.

From the above results, it may be found that when the case where the electrode array on the side close to the tumor and the back electrode array are grounded is used, as compared with the case where only the back electrode array is grounded, it is able to increase the field strength in the tumor region, increase the field strength coverage of the electric field generated between the electrode arrays, thereby to further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

In addition, as shown in <FIG>, in the case of Tumor T1, Tumor T2, Tumor T3 and Tumor T4, two electrode arrays are placed at a left-of-center position and a right-of-center position of the back respectively. Two cases in presented Table <NUM> are as follows.

It is observed that two second electrode arrays <NUM> with the low-voltage signal are arranged on the back, as compared with a case where only one second electrode array <NUM> with the low-voltage signal is arranged on the back, it is also able to increase the field strength at the tumor. Table <NUM> shows the comparison of EAUC values at the four aforementioned tumor models between the case where one second electrode array <NUM> is arranged on the back and the case where two second electrode arrays <NUM> are arranged on the back.

From Table <NUM>, it may be derived that, for Tumor T1, the EAUC value is increased by <NUM>% in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded. For Tumor T2, the EAUC value is increased by <NUM>% in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded. For Tumor T3, the EAUC value is increased by <NUM>% in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded. For Tumor T4, the EAUC value is increased by <NUM>% in the case where two electrode arrays are grounded, as compared with the case where the single electrode array is grounded.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T1 is shown in <FIG> and <FIG>, where a position of Tumor T1 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the back of the human body in <FIG> (e.g., in an upper part of <FIG>) is higher as compared with the intensity of the electric field in the upper part of <FIG>.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T2 is shown in <FIG> and <FIG>, where a position of Tumor T2 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the back of the human body in <FIG> (e.g., in an upper part of <FIG>) is higher as compared with the intensity of the electric field in the upper part of <FIG>.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T3 is shown in <FIG> and <FIG>, where a position of Tumor T3 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the back of the human body in <FIG> (e.g., in an upper part of <FIG>) is higher as compared with the intensity of the electric field in the upper part of <FIG>.

The distribution of the electric field in a horizontal plane of the thorax including Tumor T4 is shown in <FIG> and <FIG>, where a position of Tumor T4 is selected at the center of a tumor sphere. It may be observed from the figures that the intensity of the electric field located on the back of the human body in <FIG> (e.g., in an upper part of <FIG>) is higher as compared with the intensity of the electric field in the upper part of <FIG>.

Based on the above, when the quantity of electrodes with the high-voltage signal is maintained, as the quantity of electrodes with the low-voltage signal increases, the field strength coverage of the electric field generated between the electrode arrays is increased, thereby to further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

In the embodiments of the present application, when the quantity of electrodes with the first electrical signal (high voltage signal) is maintained, the more the quantity of electrodes with the second electrical signal (low voltage signal), the more the electric fields generated between the electrodes with the first electrical signal and the electrodes with the second electrical signal, the larger the coverage area of the electric fields on the target biological tissue region, so as to increase the intensity of the electric field covering the target biological tissue region, thereby to increase the intensity of the electric field covering the target biological tissue, and further improve the effect of inhibiting the division of such target biological tissue as diseased cells.

Based on the same inventive concept, the embodiments of the present application provide a computer-readable storage medium having a computer program stored thereon, the computer program implements, when executed by a processor, the control method for the electric field generating device in any of the above optional embodiments of the present application.

The computer-readable storage medium in the embodiments of the present application is applicable for various optional embodiments of the control method for the electric field generating device. The computer-readable storage medium may be a non-volatile readable storage medium or a volatile readable storage medium, which is not particularly defined herein.

When the embodiments of the present application are implemented, at least the following beneficial effects can be achieved.

As can be appreciated by a person skilled in the art, steps, measures and schemes in various operations, methods and processes that have already been discussed in the embodiments of the present application may be replaced, modified, combined or deleted. In a possible embodiment of the present disclosure, the other steps, measures and schemes in various operations, methods and processes that have already been discussed in the embodiments of the present application may also be replaced, modified, rearranged, decomposed, combined or deleted. In another possible embodiment of the present application, steps, measures and schemes in various operations, methods and processes that are known in the related art and have already been discussed in the embodiments of the present application may also be replaced, modified, rearranged, decomposed, combined or deleted.

Such words as "first" and "second" are merely for illustrative purposes, rather than to implicitly or explicitly indicate the number of the defined technical features. In this regard, the technical features defined with such words as "first" and "second" may implicitly or explicitly include one or more technical features. Further, such a phrase as "a plurality of" is used to indicate that there are at least two, e.g., two or three, components, unless otherwise specified.

It should be further appreciated that, although with arrows, the steps in the flow charts may not be necessarily performed in an order indicated by the arrows. Unless otherwise defined, the order of the steps may not be strictly defined, i.e., the steps may also be performed in another order. In addition, each of at least parts of the steps in the flow charts may include a plurality of sub-steps or stages, and these sub-steps or stages may not be necessarily performed at the same time, i.e., they may also be performed at different times. Furthermore, these sub-steps or stages may not be necessarily performed sequentially, and instead, they may be performed alternately with the other steps or at least parts of sub-steps or stages of the other steps.

Claim 1:
An electric field generating device, comprising
n electrodes (<NUM>), configured to surround a target biological tissue region in a set manner; where n is an integer not less than <NUM>;
an electrical signal generator (<NUM>), electrically connected to the n electrodes (<NUM>);
a control signal generator (<NUM>), electrically connected to the electrical signal generator (<NUM>), and configured to control the electrical signal generator (<NUM>) to apply a first electrical signal to m electrodes of the n electrodes (<NUM>), and apply a second electrical signal to at least two electrodes of n-m electrodes, to generate an electric field between the electrodes with the first electrical signal and the electrodes with the second electrical signal; wherein a voltage of the second electrical signal is less than a voltage of the first electrical signal, <NUM>≤m<n, and m is an integer;
wherein the quantity of electrodes with the first electrical signal is smaller than the quantity of electrodes with the second electrical signal.