Patent Application
20240131352
The present disclosure relates to an apparatus for treating a cancerous target site. More specifically, the present disclosure relates to an apparatus configured to provide a non-ionizing alternating electromagnetic field and local heating at the target site. The disclosure also relates to associated methods for treating a cancerous site and compositions for use in treating a cancerous target site.
Non-invasive methods of treating cancer are important methods, particularly for cancers such as glioblastoma which are difficult to remove by surgery. There is a desire for new non-invasive methods of treating cancer which effectively reduce or eliminate the cancerous cells from a target site in the body.
Radiotherapy is a type of cancer therapy which uses ionizing radiation to kill malignant cells at a target site. The ionizing radiation is provided to the target site, which causes damage by the direct or indirect action of radiation on DNA and other cell molecules. In the direct action, the radiation hits e.g. the DNA molecule directly, disrupting its molecular structure. Such structural change leads to cell damage or even cell death, and thus provides a mechanism for treatment of malignant cells.
Another form of treatment, known as alternating electric field therapy or tumour treating fields (TT-Fields) applies non-ionizing electric fields to the target site. The mechanism of TT-Fields which renders it useful for cancer treatment is different to that of radiotherapy. In particular, during the formation of mitotic spindles, the microtubule assembly deforms. Mitosis of tumour cells remains in the interdivision stage for a long time. When the cleavage furrow forms in mid to late mitosis, all polar molecules and dipoles in cells undergo di-electrophoresis under the action of TT-Fields, which accumulates in the cleavage furrow and eventually causes the cell membrane to rupture. Mitotic outcomes elicited by TT-Fields application include abnormal chromosome segregation, which triggers different forms of cell death.
Hyperthermia is a known method for treating a cancerous site. However, it can be difficult to target the cancerous site effectively. On the one hand, tissue surrounding the area being treated may also be affected by hyperthermia, particularly when the cancerous site is heated to a high temperature. On the other hand, the cancerous site may not be effectively destroyed if the site is not heated to a sufficiently high temperature. Further, whilst applying heat to a cancerous site may cause cell damage and even cell death at the cancerous site, if the heat is not correctly and accurately applied to the cancerous site in the correct dose, the cancerous site may be resistant to such heating. For example, if the hyperthermia heats up the healthy surrounding tissue in addition to the cancerous growth, blood flow will be enhanced, and nutrients supply to the cancerous growth may be higher. Thus, under some circumstances the high blood flow as a result of heating helps the dissemination of nutrients which could reach the cancerous site and therefore have the opposite intended effect, or at least result in an ineffective treatment. Further, different phases in the cell cycle of cancerous cells have been observed to have different resistances to heating. Yet further, temperature elevations in cells transiently upregulate heat shock genes that encode a class of heat shock proteins (HSPs). The mechanism responsible for the heat shock response is an autoregulatory loop; HSPs normally keep the responsible transcription factor (HSF-1) inactive but upon heating HSP bind with higher affinity to unfolded proteins, triggering the release of HSF-1 from HSP which initiates HSP gene transcription. Once the protein damage/aggregation is restored after the heat shock by the HSP, substrate-free HSP themselves may be involved in attenuating the response by rebinding HSF-1. As a result, HSP levels transiently rise after heating but also gradually decline again upon prolonged stress-free periods. The upregulation of HSP is closely associated with a transient resistant state of cells towards a subsequent second heat shock. It is thought that the elevated HSP levels, by their chaperone activity, protect cells against protein damage induced by further heating. Accordingly, there is a need to provide hyperthermia which provides the required heating to the cancerous site more accurately and reliably, in order to avoid any resistance to heating of the cancerous cells as a result of deviation from the required amount of applied heat.
Many methods of hyperthermia require a mediator (such as a nanoparticle fluid) to be administered to the site. The mediator is then heated, for example by an electric field, which then indirectly heats the target site. The mediator may be heated using an electric field which has the same or similar frequency range as TT-fields. This may be seen as advantageous as the cancerous site is attacked both via hyperthermia and via the TT-field mechanism. However, as the mediator is a fluid injected into the patient's body, the location of heating when the electromagnetic radiation is administered is hard to control.
There is a desire to find more effective cancer treatment methods for the above methods of treatment.
The present invention confronts the problem of providing more effective cancer treatment methods by providing an apparatus for treating a cancerous target site, comprising:
It is herein noted that the heat source may be any heat source which heats a specific target site without the use of a mediator (e.g. directly and not indirectly via a mediator).
In a preferred embodiment, the apparatus is configured to provide the non-ionizing alternating electromagnetic field at the target for a first time period, and to provide the direct heating at the target site for a second time period. The second time period may partially or fully overlap with the first time period. For example, the first time period may begin at the same time as the second time period, or may begin a predetermined amount of time after the first time period begins, or may begin when the first time period expires. It is preferred that the first and second time periods completely overlap so that the TT-Fields and heating are applied to the site simultaneously, providing a synergistic effect on the cells in the target site as discussed in further detail below.
It is noted that the sequence of the first and second time periods may be repeated two or more times. For example, the apparatus may be configured to apply the non-ionizing alternating electromagnetic field for a first time period, and apply the heating for a second time period a predetermined time after the first period begins. Subsequently, the apparatus may be configured to, again, apply the non-ionizing alternating electromagnetic field for a first time period, and apply the heating for a second time period the predetermined time after the first period begins. The length of the first and second time periods, and their start times relative to each other, may be configurable by a user or according to one or more schedules saved in a memory of the apparatus.
Preferably, the apparatus is configured to provide the non-ionizing alternating electromagnetic field at the target site for a first time period of between 1 minute and 24 hours.
In another preferred embodiment, the apparatus is further configured to provide the heating at the target site for a second time period of between 1 minute and 360 minutes. The heating may be applied simultaneously to the non-ionizing alternating electromagnetic field for a third time period. The third time period may be all or part of the second time period.
In another preferred embodiment, the electromagnetic emitter is configured to provide an alternating electromagnetic field having a frequency of between 10 kHz to 500 kHz and more preferably between 10 kHz and 300 kHz, and even more preferably 100 kHz to 300 kHz. It is observed that the therapeutic effect of the tumour-treating field is significantly increased when the frequency is below 300 kHz.
In another preferred embodiment, the electromagnetic emitter is configured to provide an alternating electromagnetic field at the target site having a magnetic flux density of between 0.1 pT and 1 mT, or between 0.1 pT and 100 μT, or between 100 μT and 1 mT and/or an electric field strength of between 1 V/cm and 3 V/cm.
In another preferred embodiment, electromagnetic emitter is configured to provide an alternating electromagnetic field at the target site having a magnetic flux density of between 0.5 μT and 1 mT, and more preferably between 8 μT and 1 mT.
In another preferred embodiment, the heat source is configured to heat the target site to a temperature of at least 42° C. and preferably between 42° C. and 57° C. Heating the target site to a temperature of at least 42° C. induces heating effects on the target site which corresponds to extreme hyperpyrexia.
In another preferred embodiment, the heat source comprises an ultrasonic emitter configured to provide ultrasound radiation to the target site, optionally wherein the ultrasound radiation has one or more focal areas in the target site. The one or more focal areas may be provided from a single transducer or a plurality of transducers.
In a further preferred embodiment, the heat source comprises one or more of:
In a still further preferred embodiment, the apparatus additionally comprises an electronic controller for electronically controlling the electromagnetic emitter and the heat source.
A further aspect of the present invention refers to a method for treating a cancerous target site using an apparatus according to the supra embodiments, wherein the apparatus may take any configuration disclosed therein and wherein the method is preferably implemented by suitably positioning the emitter 10 and heat source 20 on the patient. For example, the applicators of the electromagnetic emitter 10 may be placed at predetermined points on the patient's body and the heat source 20 (for example the transducer 204 described in relation to
In step S1, the non-ionizing alternating electromagnetic field is provided to give a magnetic flux density at the target site using electromagnetic emitter 10.
In step S2, the heat (and more particularly direct heat) is provided to the target site using heat source 20. This may be provided whilst the electromagnetic field is also being provided to the target site 30 or within a predetermined time before or after the electromagnetic field is provided. In some embodiments, it may be that only the alternating electromagnetic field is provided to produce the magnetic flux density at the target site without the heating for a first time period, before both are provided simultaneously to the target site.
Optionally, in step S3, an anti-carcinogenic composition is provided to the target site. The anti-carcinogenic composition may be administered by any suitable means, such as orally or intravenously. It is noted that the anti-carcinogenic composition may be provided before or simultaneously to steps S1, S2 and step S4 or a predetermined time after step S1, S2 or S4.
Examples of anti-carcinogenic compositions that may be used to implement the present invention are described in detail throughout the present invention.
Also optionally, in step S4, a Glutathione (GSH) depleting composition is provided to the target site in addition to the anti-carcinogenic compound. The GSH depleting composition may be administered by any suitable means, such as orally or intravenously. It is noted that the GSH depleting composition may be provided before or simultaneously to steps S1, S2 and step S3 or a predetermined time after step S1, S2 or S3, preferably at a predetermined time after step S3. Examples of GSH depleting compositions that may be used to implement the present invention are described in detail throughout the present invention.
In step S5, the direct heating is stopped and in step S6 the non-ionizing alternating electric field is stopped. It is noted that steps S5 and S6 may occur simultaneously or the direct heating may be stopped before the non-ionizing alternating electromagnetic field is stopped, such that only the non-ionizing alternating electromagnetic field is applied for a predetermined time after the direct heating is stopped.
A still aspect of the present invention, refers to an anti-carcinogenic composition for use in a method for treating a cancerous target site using an apparatus according to the supra embodiments, wherein the apparatus may take any configuration disclosed therein and wherein the method is preferably implemented by suitably positioning the emitter 10 and heat source 20 on the patient. For example, the applicators of the electromagnetic emitter 10 may be placed at predetermined points on the patient's body and the heat source 20 (for example the transducer 204) may also be suitably positioned. Wherein the method comprises:
In step S1, the non-ionizing alternating electromagnetic field is provided to give a magnetic flux density at the target site using electromagnetic emitter 10.
In step S2, the heat (and more particularly direct heat) is provided to the target site using heat source 20. This may be provided whilst the electromagnetic field is also being provided to the target site 30 or within a predetermined time before or after the electromagnetic field is provided. In some embodiments, it may be that only the alternating electromagnetic field is provided to produce the magnetic flux density at the target site without the heating for a first time period, before both are provided simultaneously to the target site.
In step S3, an anti-carcinogenic composition is provided to the target site. The anti-carcinogenic composition may be administered by any suitable means, such as orally or intravenously. It is noted that the anti-carcinogenic composition may be provided before or simultaneously to steps S1, S2 and step S4 or a predetermined time after step S1, S2 or S4. Examples of anti-carcinogenic compositions that may be used to implement the present invention are described in detail through out the present invention.
Optionally, in step S4, a Glutathione (GSH) depleting composition is provided to the target site in addition to the anti-carcinogenic compound. The GSH depleting composition may be administered by any suitable means, such as orally or intravenously. It is noted that the GSH depleting composition may be provided before or simultaneously to steps S1, S2 and step S3 or a predetermined time after step S1, S2 or S3, preferably at a predetermined time after step S3.
Examples of GSH depleting compositions that may be used to implement the present invention are described in detail through out the present invention.
In step S5, the direct heating is stopped and in step S6 the non-ionizing alternating electric field is stopped. It is noted that steps S5 and S6 may occur simultaneously or the direct heating may be stopped before the non-ionizing alternating electromagnetic field is stopped, such that only the non-ionizing alternating electromagnetic field is applied for a predetermined time after the direct heating is stopped.
Embodiments will now be explained in detail, by way of non-limiting example only, with reference to the accompanying figures described below.
The present invention related to an apparatus which is configured to provide both a non-ionizing alternating electromagnetic field and hyperthermia to a target site, wherein the electromagnetic field and hyperthermia can be provided independently. The electromagnetic field may be applied, for example, by means of a magnetic applicator that provides a magnetic flux density in the target site. In hyperthermia treatments involving a mediator, such an alternating electromagnetic field is provided which also may be absorbed by the mediator. However, as the mediator absorbs the electromagnetic energy, the tumour-treating effects of the electromagnetic field may be reduced. The present invention overcomes this problem by providing hyperthermia independently such that both treatments can be provided to the cancerous site without reducing the effectiveness of the other. In the present invention, the tumour-treating effects are due to a combined application of electromagnetic fields with direct hyperthermia. The electromagnetic field may be introduced with a magnetic field applicator. In some further examples of the present disclosure, the treatment may further include the administration of an anti-cancer composition.
As used herein, the term “tumour treating field”, “TT-Field” or “TTF” may be understood to mean an oscillating electromagnetic field applied to a target site. In particular, the electromagnetic field is generated by applicators which are electrically isolated from the target site so that electrical current does not flow between the target site and the applicators.
As disclosed herein, hyperthermia may be defined as elevation to a temperature above 37.5° C. Accordingly, the apparatuses disclosed herein may be configured to heat a target site to temperatures above 37.5° C. It is noted that hyperthermia is defined as a temperature greater than between 37.5° C. to 38.3° C. (depending on the reference used), occurring without a change in the body's temperature set point. In contrast, hyperpyrexia is an extreme elevation of body temperature which, depending upon the source, is classified as a core body temperature greater than or equal to 40.0 or 41.0° C.; the range of hyperpyrexias include cases considered severe (≥40° C.) and extreme (≥42° C.). It differs from hyperthermia in that one's thermoregulatory system's set point for body temperature is set above normal, then heat is generated by the body to achieve it. In contrast, hyperthermia involves body temperature rising above its set point due to outside factors.
Further, it is noted that thermal ablation is a type of procedure that uses heat, cold, microwave and electrical currents to vaporize (ablate) cancer cells and tumors by heating to above >50° C.
In preferred embodiments, the apparatus is configured to heat the target site to a temperature of between 39° C. and 52° C. (heating to above 39° C. may increase the sensitivity of a cancerous growth to other therapies such as TT-fields, chemotherapy and radiotherapy) and preferably at least 41.1° C. (above which, advantageously, irreversible damage is caused to cells). It is preferred that the heat source is configured to heat the target site to a temperature of at least 42° C. and preferably between 42° C. and 57° C. Heating the target site to a temperature of at least 42° C. induces heating effects on the target site which corresponds to extreme hyperpyrexia.
The heat source 30 may be any suitable heat source for providing direct heating to the target site 30, and may comprise electromagnetic heating, such as capacitive radiofrequency heating, radiative radiofrequency heating, microwave heating, infrared heating and laser heating, heating by ultrasound, heating via a heated fluid, heating by conductive heat emitter, or any other suitable method which heats the target site 30 independently of the non-ionizing alternating electromagnetic field 15. The heat source 30 may be any heat source which heats the target site without the use of a mediator (e.g. directly and not indirectly via a mediator).
In any of the embodiments disclosed herein, the electromagnetic emitter 10 may be configured to provide an electromagnetic field 15 having a frequency of between 10 kHz to 500 kHz and more preferably between 10 kHz and 300 kHz. The electromagnetic field may have a magnetic flux density of between 0.1 pT and 1 mT, or between 0.1 pT and 100 μT, or between 100 μT and 1 mT, and/or the corresponding electric field of between 1 V/cm and 3 V/cm depending on the tissue impedance (i.e. taking into account possible attenuation of the field as it travels from the electromagnetic emitter 10 to the target site 30, which can be determined from the impedance arising from the different types of tissue present between the electromagnetic emitter 10 and the target site 30). As noted above, the electromagnetic field 15 is non-ionizing, and its mechanism on the cancerous site is different to that of ioinizing radiation as discussed in the background section of the present disclosure. Further, the electromagnetic field 15 itself does not provide direct heating to the target site 30 due to the relatively low intensity of the oscillating field.
It will be appreciated that in any of the embodiments disclosed herein the electromagnetic emitter 10 and heat sources may be powered by any power source, and may be powered by the same or different power sources. Likewise, each of the electromagnetic emitter 10 and the heat source 20 may comprise a user interface for selecting the operating parameters of each emitter (frequency, field strength, amplitude, etc), or the emitter 10 and heat source 20 may comprise pre-programmed sequences for emitting electromagnetic radiation and heat according to a predetermined program selectable by the user.
In any of the embodiments disclosed herein, the apparatus may further comprise a thermometry element for measuring the temperature of the target site 30. For example, the apparatus may comprise an implantable thermometry probe configured to be implanted proximal to the target site 30 to measure a temperature indicating the temperature of the target site 30. The probe may comprise, for example, thermocouples, thermistors and/or fibreoptic sensors. In other embodiments, non-invasive thermometry such as infrared sensing, CT thermometry, or magnetic resonance thermometry may be used.
The electromagnetic emitter 10 may comprise one or more sources 12 (such as one or more current or voltage sources) electrically connected to one or more applicators 14. The applicators 14 may be configured to be placed on or proximal to the surface of the patient body 35 and are electrically insulated from the patient body (i.e. do not form a closed electrical circuit between the source 12 and the patient body). In some embodiments, the applicators 14 may comprise one or more electrodes with an electrically insulating coating for preventing electrical contact between the electrodes and the surface of the patient and thus the target site. It is noted that even if the applicators are placed on the surface of the patient of the patient body 35, they remain electrically insulated from the body by, for example, the presence of the electrically insulating coatings. The source 12 may be configured to provide an alternating electromagnetic field to the applicators 14, which in turn produce a magnetic flux density towards the target site 30 to provide the non-ionizing alternating electromagnetic field 15 at the target site 30. It will be appreciated that any number of applicators 14 may be used depending on the type of target site, and the strength of the resulting magnetic flux density at the target site 30 can be readily calculated from the setup by superposition of the electromagnetic fields emitted by each applicator 14. In some embodiments, the applicators 14 may comprise a coil with positive and negative terminals. The one or more sources may be configured to provide an alternating current through the coil to generate a magnetic field out of the coil. The coil may comprise any number of turns, for example 1, 2, 3, 4, 5, 6, 7, 8, 9, 10, 15, 20, 25, 50 or 100, 500 or more.
The heat source 200 shown in
The ultrasound emitter 200 may be configured to provide acoustic energy at frequencies between 0.5 and 10 MHz to provide heating at the target site 30.
In some embodiments, the ultrasound emitter 200 may comprise one or more multi-transducer arrays or phased arrays, planar devices or bowl-shaped sources. Further, the ultrasound emitter 200 may be configured to emit the ultrasound radiation interstitially. That is, the ultrasound emitter 200 may comprise one or more catheter-mounted transducers or other emitting components which are configured to be inserted into the body 35 at or near the target site 30, in order to emit ultrasonic radiation towards one or more points at the target site 30 to provide the required heating.
Whilst
The ultrasound emitter 200 is configured to emit ultrasound radiation 205 to the target site 30 to cause heating at the target site. In particular, the ultrasound emitter 200 is configured to heating the target site to a predetermined temperature, preferably a temperature of 42° C. or less, and maintain the temperature at the predetermined temperature whilst the electromagnetic field is applied. It will be appreciated that the ultrasound emitter 200 may be configured to heat the target site 30 by providing ultrasound radiation having a predetermined frequency and amplitude which causes the required heating at the target site 30. The ultrasound radiation may be continuous or pulsed wave. For a given frequency, amplitude and type of ultrasonic radiation, the amount of heating at a target site can be determined by routine experimentation.
It will be appreciated for the embodiment of
The heat source 300 comprises one or more antennas or applicators 304 configured to provide an electromagnetic field 305 for providing direct heating to the target site 30. The heat source 300 comprises one or more electromagnetic sources 302 for driving one or more antennas or applicators 304 to provide the heating electromagnetic field 305. The electromagnetic field 305 has a field strength and frequency which causes heating of the target site. The frequency of the electromagnetic field 305 is sufficiently different (e.g. at least an order of magnitude difference) such that the electromagnetic fields 305 and 15 interact with the target site 30 independently (i.e. such that the electromagnetic interference between the fields is negligible). The frequency of the electromagnetic field 305 may be, for example, above 1 MHz to cause dielectric heating of the target site 30 by molecular dipole rotation, polarization and/or vibration, or Ohms law.
The number and configuration of antennas or applicators 304, including their positions, relative amplitudes and phases, can be selected in order to create constructive and/or destructive interference and cause heating only over a particular volume including the target site 30. For example, the antennas or applicators 304 may comprise a single antenna, a pair of antennas, and a 2D or 3D array or phased array of antennas.
In some embodiments, the electromagnetic source 302 is a radiofrequency (RF) source configured to operate at a frequency between 8 and 30 MHz (for example, 8 MHz, 13.56 MHz or 27.12 MHz) to cause capacitive heating. The one or more antennas or applicators 304 comprise a pair of metal applicators with the target site 30 placed between the applicators.
Optionally, the applicators may be coupled to water bolus bags or other media for transferring the field into the body 35. When the RF field is applied to the applicators, power is transferred to the target site 30 and heating is caused. This technique may be used for both superficial and deep tumours by selecting different configurations of applicators to concentrate the resulting electric field at the target site 30. Alternatively, the applicators may be provided as coplanar, or one or more applicators may be configured to be placed inside the body 35 inside insulating catheters. A single applicator may instead be used, coupled to an external ground plane. In all of these configurations, the RF field generated at the target site causes direct heating.
In some embodiments, the electromagnetic source 302 is an RF source configured to operate at frequencies between 60 MHz and 150 MHz. The one or more antennas or applicators 304 comprise one or more antennas placed external to the body. The electromagnetic fields generated at this frequency range penetrate deep into the body and so are suitable for heating of deep target sites 30. Again, the one or more antennas may comprise a pair of antennas with the target site 30 placed between. The antennas may be coupled to water bolus bags or other media for transferring the electromagnetic field into the body 35
In some embodiments, the electromagnetic source 302 is a microwave (MW) source configured to operate at frequencies between 400 MHz and 2.5 GHz (for example 433 MHz, 915 MHz or 2.45 GHz). The one or more antennas may comprise a pair of antennas or one or more antenna arrays with the target site 30 placed between. The antennas may again be coupled to water bolus bags or other media for transferring the electromagnetic field into the body 35.
It will be appreciated for the embodiment of
The heat source 400 comprises an electromagnetic source 402 and one or more electromagnetic emitters 404 configured to penetrate the body 35 such that a distal portion of the emitters can be positioned within the target site 30. The one or more emitters 404 are electrically connected to the electromagnetic source 402 so that an electrical current is applied to the one or more emitters 404. The one or more emitters 404 may comprise one or more monopole, dipole, slot or helical coil microwave antennas, resistively-coupled radiofrequency, local current field electrodes or capacitively coupled radiofrequency catheter-based electrodes. Capacitively coupled electrodes may be configured to be contained in low-loss catheters such as a Nylon or Teflon catheter.
In some embodiments, the electromagnetic source 402 is configured to provide an alternating electric current to the one or more emitters 404 in the frequency range of 350 kHz to 30 MHz, which induces an electric current in the area of tissue near the needle(s) and as a result heats the tissue. In other embodiments, the electromagnetic source 402 is configured to provide an alternating electric current to the one or more emitters 404 in the frequency range of 900 MHz to 2.5 GHz (for example 915 MHz or 2.45 GHz), which causes dielectric heating of the tissue surrounding the needle(s).
In other embodiments, the emitters 404 comprise a plurality of electrodes configured to be implanted around the target site 30, and the electromagnetic source 402 is configured to provide a series of very short (e.g. about 100 μs) direct-current electrical pulses between the electrodes. The voltage of the pulses and the positioning of the electrodes are configured to provide a high field strength (e.g. between about 100 V/cm to 3000 V/cm). It has been observed that such pulses provide heating to the target site 30.
It will again be appreciated for the embodiment of
The heat source 500 comprises one or more infrared light source 504 configured to provide infrared radiation 505 to the target site 30, and a power source 502 for powering the one or more infrared lamps. The infrared light source 504 may emit infrared light of any frequency, and in particular frequencies above 300 GHz. The penetration depth of the infrared radiation is typically 1 cm or less, so this apparatus may be suitable for target sites 30 which is located superficially in the body 35.
Again, the power output of the power source 502 as well as the duration of application of the radiation may be selected in order to arrive a predetermined amount of heating at the target site 30. This may be determined by prior empirical measurement or the apparatus may additionally include a thermometer component for measuring the temperature of the target site 30, with heat being applied to achieve and maintain a target temperature at the target site 30.
The heat source comprises a laser source 604 and a power source 602 configured to power the laser source. The laser source 604 may be configured to emit laser radiation to the target site 30 to cause heating at the target site. The laser radiation may be optically guided, by an optical fiber, directly to the target site to cause local ablation of the target site 30. The laser source 604 may be configured to emit laser radiation having a wavelength of between 900 nm and 1100 nm at any suitable intensity for causing the required heating at the target site 30. The laser source 604 may be configured to operate at between 0.5 W and 15 W power (for example 980 nm at 15 W or 1064 nm at 12 W). The laser source 604 may be moved rotationally and linearly to target multiple regions in one or more target sites 30.
The power output of the power source 602 as well as the duration of application of the laser radiation may be selected in order to arrive a predetermined amount of heating at the target site 30. This may be determined by prior empirical measurement or the apparatus may additionally include a thermometer component for measuring the temperature of the target site 30, with heat being applied to achieve and maintain a target temperature at the target site 30. For example, the apparatus may include an Mill machine to perform magnetic resonance thermometry to monitor the temperature of the target site 30 during the heating process.
The heat source 700 comprises a heater 702, a pump 704, a fluidic output 706 and a fluidic input 708. The fluidic output 706 is configured to fluidically connect to a part the body 35 which is upstream from the target site 30, and the fluidic input 708 is configured to fluidically connect to a part of the body 35 which is downstream from the target site 30. When connected, a fluidic loop is created from the target site 30 to the pump 704 and back to the target site 30 again. The fluidic loop may be configured to be created in any fluidic system of the body 35 (e.g. vascular, renal or similar). The heater 702 is configured to heat the fluid to a desired temperature as it passes through the heat source 700, which is then delivered to the target site 30 via fluidic output 706. Accordingly, the fluidic loop provides a continuous source of heated fluid to the target site 30. It is noted that the fluid may be the patient's blood or additionally the heat source 700 may comprise a reservoir of fluid (not shown) which is configured to be heated and added to the fluidic loop. For example, the fluid may comprise a chemotherapeutic composition, anti-cancer drug or similar or may comprise a biocompatible solution such as saline solution or similar.
The heater 702 may be any suitable heater, such as a resistive heater, or an electromagnetic heater configured to heat the fluid by the emission of, for example, microwave radiation. The heater 702 may be situated externally to the body 35 or may be configured to be implanted in the body 35.
The amount of heat provided by the heat source 700 as well as the duration of application of the heat source 700 may be selected in order to arrive a predetermined amount of heating at the target site 30. This may be determined by prior empirical measurement or the apparatus may additionally include a thermometer component for measuring the temperature of the target site 30, with heat being applied to achieve and maintain a target temperature at the target site 30.
The heat source 800 comprises a heater 802, a reservoir 805, a pump 804 and a fluidic output 806. The fluidic output 806 is configured to be fluidically connected to the target site 30. In use, the pump 804 is configured to pump fluid in the reservoir 805 to the target site 30 via fluidic output 806. The heater 802 is configured to heat the fluid in the reservoir 805 to a desired temperature before the fluid is pumped to the target site 30. The fluid may comprise a chemotherapeutic composition, anti-cancer drug or similar or may comprise a biocompatible solution such as saline solution or similar.
The amount of heat provided by the heat source 800, the amount of fluid provided from the reservoir 805 and the duration of application of the heat source 800 may be selected in order to arrive a predetermined amount of heating at the target site 30. This may be determined by prior empirical measurement or the apparatus may additionally include a thermometer component for measuring the temperature of the target site 30, with heat being applied to achieve and maintain a target temperature at the target site 30.
The applicators 14 may be configured to be placed on the surface of the patient body 35. The electromagnetic source 12 may be configured to provide an alternating electromagnetic field to the applicators 14, which in turn produce a magnetic flux density towards the target site 30 to provide the non-ionizing alternating electromagnetic field 15 at the target site 30. It will be appreciated that any number of applicators 14 may be used depending on the type of target site, and the strength of the resulting magnetic flux density at the target site 30 can be readily calculated from the setup by superposition of the electromagnetic fields emitted by each applicator 14.
Heat source 900 comprises a heat emitter 904 configured to provide conductive heating to the target site 30. The heat source may comprise a power source 902 to power the heat emitter 904 (such as an electrical power source), or the heat emitter 904 may be pre-heated or chemically self-heating (e.g. by exothermic chemical reaction). The heat emitter 904 may be provided on the surface of the body 35, or may be configured to be implanted inside the body to provide heat to the target site 30 at a location proximal to the target site. For example, the heat emitter 904 may be an implantable resistive heater configured to be powered by an electrical power source 902. The heat emitter 904 may be configured to heat a local region of the body 35 or it may be configured to heat the entire body 35.
The amount of heat provided by the heat source 900, and the duration of application of the heat source 900 may be selected in order to arrive a predetermined amount of heating at the target site 30. This may be determined by prior empirical measurement or the apparatus may additionally include a thermometer component for measuring the temperature of the target site 30, with heat being applied to achieve and maintain a target temperature at the target site 30.
The apparatus 1 shown in
The controller 40 further comprises one or more of a user interface 43, memory 44 and processor 45. The user interface 43 allows a user to control operation of the emitter 10 and heat source 20 manually, for example by controlling the operating parameters of the emitter 10 and heat source 20, and switching on or off their operation. The user interface 43 may allow the user to select a sequence of operation of the emitter 10 and heat source 20 over a time period. The memory 44 may contain instructions, which when executed using the processor 45, cause the emitter 10 and heat source 20 to be operated according to any suitable sequence including the sequences of operation disclosed herein.
The memory 44 may comprise one or more volatile or non-volatile memory devices, such as DRAM, SRAM, flash memory, read-only memory, ferroelectric RAM, hard disk drives, floppy disks, magnetic tape, optical discs, or similar. Likewise, the processor 45 may comprise one or more processing units, such as a microprocessor, GPU, CPU, multi-core processor or similar.
The controller 40 may further be implemented in software, hardware, or any combination in order to execute the sequences of operation disclosed herein.
In step S1, the non-ionizing alternating electromagnetic field is provided to give a magnetic flux density at the target site using electromagnetic emitter 10.
In step S2, the heat (and more particularly direct heat) is provided to the target site using heat source 20. This may be provided whilst the electromagnetic field is also being provided to the target site 30 or within a predetermined time before or after the electromagnetic field is provided. In some embodiments, it may be that only the alternating electromagnetic field is provided to produce the magnetic flux density at the target site without the heating for a first time period, before both are provided simultaneously to the target site.
Optionally, in step S3, an anti-carcinogenic composition is provided to the target site. The anti-carcinogenic composition may be administered by any suitable means, such as orally or intravenously. It is noted that the anti-carcinogenic composition may be provided before or simultaneously to steps S1, S2 and step S4 or a predetermined time after step S1, S2 or S4.
The term “anti-carcinogenic composition”, as used herein, refers to a composition that comprises an agent that at least partially inhibits the development or progression of a cancer, including inhibiting in whole or in part symptoms associated with the cancer. The term “cancer”, a used herein, refers to a disease characterized by uncontrolled cell division (or by an increase of survival or apoptosis resistance) and by the ability of said cells to invade other neighbouring tissues (invasion) and spread to other areas of the body where the cells are not normally located (metastasis) through the lymphatic and blood vessels, circulate through the bloodstream, and then invade normal tissues elsewhere in the body. Depending on whether or not they can spread by invasion and metastasis, tumours are classified as being either benign or malignant: benign tumours are tumours that cannot spread by invasion or metastasis, i.e., they only grow locally; whereas malignant tumours are tumours that are capable of spreading by invasion and metastasis. The anti-carcinogenic composition may comprise one or more anti-carcinogenic compositions, including one or more of those disclosed in relation to
As used herein, the term cancer, is preferably directed to solid tumours and/or infiltrating tumours.
As used herein, a “solid tumour” is understood as an abnormal mass of tissue that usually does not contain cysts or liquid areas. Different types of solid tumours are named for the type of cells that form them. Examples of solid tumours are sarcomas, carcinomas, and lymphomas. Leukemias (cancers of the blood) generally do not form solid tumours.
As used herein, an “infiltrating tumour” is understood as tumours that have abnormal structures of tumours that show, at the same time, clear growing nodules and infiltrating growth.
Preferably the invention is directed to cancers including, but not limited to, the following types: breast cancer; biliary tract cancer; bladder cancer; brain cancer including glioblastomas, in particular glioblastoma multiforme, and medulloblastomas; cervical cancer; head and neck carcinoma; choriocarcinoma; colon cancer, colorectal cancer; endometrial cancer; esophageal cancer; gastric cancer; intraepithelial neoplasms including Bowen's disease and Paget's disease; liver cancer, hepatoma; lung cancer, pleural mesothelioma; oral cancer including squamous cell carcinoma; parotid gland cancer; ovarian cancer including those arising from epithelial cells, stromal cells, germ cells and mesenchymal cells; pancreatic cancer; prostate cancer; kidney cancer, suprarenal cancer; rectal cancer; sarcomas including leiomyosarcoma, rhabdomyosarcoma, liposarcoma, fibrosarcoma, and osteosarcoma; skin cancer including melanoma, Merkel cell carcinoma, Kaposi's sarcoma, basal cell carcinoma, and squamous cell cancer; cervix cancer, endometrial cancer; testicular cancer including germinal tumors such as seminoma, non-seminoma (teratomas, choriocarcinomas), stromal tumors, and germ cell tumors; thyroid cancer including thyroid adenocarcinoma and medullar carcinoma; and renal cancer including adenocarcinoma and Wilms tumor.
In a particular embodiment, the cancer is melanoma. The term “melanoma”, as used herein, refers to a malignant skin tumour of melanocytes and includes, but is not limited to, melanomas, metastatic melanomas, melanomas derived from either melanocytes or melanocyte related nevus cells, melanocarcinomas, melanoepitheliomas, melanosarcomas, melanoma in situ, superficial spreading melanoma, modular melanoma, lentigo malignant melanoma, acral lentiginous melanoma, invasive melanoma and familial atypical mole and melanoma (FAM-M) syndrome. Moreover, the term “melanoma” refers not only to primary melanomas but also to “melanoma metastasis” which, as used herein, refers to the spread of melanoma cells to regional lymph nodes and/or distant organs. This event is frequent, given that melanomas contain multiple cell populations characterized by diverse growth rates, karyotypes, cell-surface properties, antigenicity, immunogenicity, invasion, metastasis, and sensitivity to cytotoxic drugs or biologic agents. Melanoma shows frequent metastasis to brain, lungs, lymph nodes, and skin. Other cancers will-be known to one of ordinary skill in the art.
It is noted that, as already indicated previously, and as it can be seen in
Hyperthermia equivalent to a very high fever (41° C. or above) reduced the viability of U87MG cells significantly. The data labelled * indicates a P value (student's t test) less than 0.01 compared to the 37° C. data at the corresponding time, and the data labelled + indicates a P value less than 0.01 for the data at 10 minutes compared to the data at 5 mins for the same temperature.
The effectiveness of therapy by heating in combination with tumour treating fields and exposure to PT is also observed in other cell lines in vitro, such as A2058 (melanoma), AsPC-1 (pancreas carcinoma), A549 (lung carcinoma), MCF-7 (mammary gland carcinoma), HT-29 (colorectal carcinoma), PC-3 (prostate carcinoma), SK-OV-3 (ovarian carcinoma and HepG2 (hepatocarcinoma).
Comparing the data of
Table 1 shows data examining the effect of GSH depletion on cell viability for U87MG, AsPC1 and A2058 cells in vitro. For rows including “TTF”, a TT-Field was applied at 200 kHz for 240 mins (from minute 0 to minute 240) for a field intensity of 1.5 μT. For rows including “HT”, hyperthermia applied was at 42 ° C. for U87MG and 52° C. for AsPC1 and A2058 for 20 minutes (from minute 120 to minute 140). For rows including “BSO”, 1 mM of buthione sulfoximine, a specific inhibitor of GSH synthesis, was added to the cell culture medium at the time the cells of the culture were seeded. When HT and TTF were applied in combination with BSO, the HT and TTF were applied 24 hours after seeding. The data show the means and standard deviations for five independent experiments. Data labelled * has a P-value (student's t test) of less than 0.01 compared with the control data. The data labelled + has a P-value (student's t test) of less than 0.01 compared with the TTF+HT data. The data therefor indicate that GSH depletion potentiates the anticancer effect of the electromagnetic radiation and heat.
1.92 ± 0.59*+
2.49 ± 0.66*+
15.3 ± 3.9*+
2.06 ± 0.51*+
Accordingly, the use of the apparatuses disclosed herein in combination with the application of pterostilbene provides a highly effective method of treating a cancerous site, and may even entirely eliminate the cancerous cells altogether. Therefore, in one aspect, said anti-carcinogenic composition comprises (i) pterostilbene, pterostilbene phosphate or a pharmaceutically acceptable salt thereof. Alternatively, the anti-cancer composition may be provided in a cocrystal, a water-soluble prodrug, nanoparticle, nanodot, nanorob, nanospike, nanorod, nanocluster, nanoceramic, liposome or exosome formulation, or may be provided in an implantable device configured to release the anti-cancer composition when implanted in the body. Please note that said anti-carcinogenic composition may comprise any anti-oxidant composition. In this sense, the anti-carcinogenic composition may comprise any stilbenoid, apart from pterostilbene, suitable as an anti-carcinogenic agent, such as resveratrol.
The term “pterostilbene” or “Pter” or “trans-3,5-dimethoxy-4′-hydroxystilbene” as used herein, refers to a compound of formula
The term “pterostilbene phosphate” refers to a compound of formula
The term “pharmaceutically acceptable salt” refers to any salt of pterostilbene or pterostilbene phosphate which, upon administration to the recipient is capable of providing (directly or indirectly) a compound as described herein. Preferably, as used herein, the term “pharmaceutically acceptable salt” means approved by a regulatory agency of the Federal or a state government or listed in the U.S. Pharmacopeia or other generally recognized pharmacopeia for use in animals, and more particularly in humans. The preparation of salts can be carried out by methods known in the art. Illustrative non-limitative examples of pharmaceutically acceptable salts include, but are not limited to sulfate, citrate, acetate, oxalate, chloride, bromide, iodide, nitrate, bisulfate, phosphate, acid phosphate, isonicotinate, lactate, salicylate, acid citrate, tartrate, oleate, tannate, pantothenate, bitartrate, ascorbate, succinate, maleate, gentisinate, fumarate, gluconate, glucuronate, saccharate, formate, benzoate, glutamate, methanesulfonate, ethanesulfonate, benzenesulfonate, p-toluenesulfonate, and pamoate salts. The pharmaceutically acceptable salts of pterostilbene or pterostilbene phosphate are preferably prepared from a polyphenol compound having an acidic functional group, and an acceptable inorganic or organic base. Suitable bases include, but are not limited to, hydroxides of alkali metals such as sodium, potassium, and lithium; hydroxides of alkaline earth metals such as calcium and magnesium; hydroxides of other metals, such as aluminum and zinc; ammonia, and organic amines, such as unsubstituted or hydroxy-substituted mono-, di-, ortri-alkylamines, dicyclohexylamine; tributyl amine; pyridine; N-methyl, N-ethylamine; diethylamine; triethylamine; mono-, bis-, or tris-(2-hydroxy substituted lower alkylamines), such as mono-; bis-, or tris-(2-hydroxyethyl)amine, 2-hydroxy-tert-butylamine, or tris-(hydroxymethyl)methylamine, N,N-di-lower alkyi-N-(hydroxy lower alkyl)-amines, such as N,N-dimethyl-N-(2-hydroxyethyl)amine or tri-(2-hydroxyethyl)amine; N-methyl-0-glucamine; and amino acids such as arginine, lysine, and the like. The term “pharmaceutically acceptable salt” also includes a hydrate of a polyphenol compound. In a particular embodiment, the pharmaceutically acceptable salt is a disodium salt.
Further illustrative non-limitative examples of cancer chemotherapeutic agents which may be in accordance to the present invention include: alkylating agents such as nitrogen mustards/oxazaphosphorines (e.g. cyclophosphamide, ifosfamide), nitrosoureas (e.g. carmustine), triazenes (e.g. temozolamide), and alkyl sulfonates (e.g. busulfan); antimetabolite drugs (for example 5-fluorouracil, capecitabine, 6-mercaptopurine, methotrexate, gemcitabine, cytarabine, fludarabine or pemetrexed); anthracycline antibiotics such as doxorubicin and daunorubicin, taxans such as Taxol™ and docetaxel, vinca alkaloids such as vincristin and vinblastine, 5-fluorouracil (5-FU), leucovorin, irinotecan, idarubicin, mitomycin C, oxaliplatin, raltitrexed, pemetrexed, tamoxifen, cisplatin, carboplatin, methotrexate, actinomycin D, mitoxantrone, blenoxane, mithramycin, paclitaxel, 2-methoxyestradiol, prinomastat, batimastat, BAY 12-9566, carboxyamidotriazole, CC-1088, dextromethorphan acetic acid, dimethylxanthenone acetic acid, endostatin, IM-862, marimastat, penicillamine, PTK787/ZK 222584, RPI.4610, squalamine lactate, SU5416, thalidomide, combretastatin, COL-3, neovastat, BMS-275291, SU6668, anti-VEGF antibodies, Medi-522 (Vitaxin II), CAI, Interleukin 12, IM862, amiloride, angiostatin, angiostatin K1-3, angiostatin K1-5, captopril, DL-alpha-difluoromethylornithine, DL-alpha-difluoromethylornithine HC1, endostatin, fumagillin, herbimycin A, 4-hydroxyphenylretinamide, juglone, laminin, laminin hexapeptide, laminin pentapeptide, lavendustin A, medroxyprogesterone, minocycline, placental ribonuclease inhibitor, suramin, thrombospondin, antibodies targeted against proangiogenic factors (for example, bevacizumab, cetuximab, panitumumab, trastuzumab); topoisomerase inhibitors; antimicrotubule agents; low molecular weight tyrosine kinases inhibitors of proangiogenic growth factors (for example erlotinib, sorafenib, sunitinib, gefitinib); GTPase inhibitors; histone deacetylase inhibitors; AKT kinase or ATPase inhibitors; Wnt signaling inhibitors; inhibitors of the E2F transcription factor; mTOR inhibitors (for example temsirolimus); alpha, beta and gamma interferon, IL-12, matrix metalloproteinase inhibitors (for example, COL3, Marimastat, Batimastat); ZD6474, SU11248, vitaxin; PDGFR inhibitors (for example imatinib); NM3 and 2-ME2; cyclic peptides such as cilengitide. Other chemotherapy agents suitable are described in detail in The Merck Index in CD-ROM, 13rd Edition. In a preferred embodiment of the invention, chemotherapeutic agents are selected from the group consisting of docetaxel (Taxotere®), cisplatin, pemetrexed, gemcitabine and irinotecan.
In a particular embodiment, the cancer chemotherapeutic agent is a taxane, preferably which comprises or consists on paclitaxel. The term “paclitaxel”, as used herein, refers to a compound with chemical name (2α,4α,5β,7β,10β,13α)-4,10-Bis(acetyloxy)-13-{[(2R,3 S)-3(benzoylamino)-2-hydroxy-3-phenylpropanoyl]oxy}-1,7-dihydroxy-9-oxo-5,20-epoxytax-11-en-2-yl benzoate and having the chemical formula
In a more particular embodiment, the paclitaxel is protein bound paclitaxel. The term “protein-bound paclitaxel” or “nab-paclitaxel” or “nanoparticle albumin-bound paclitaxel”, as used herein, refers to a formulation in which paclitaxel is bound to albumin as a delivery vehicle.
The cancer chemotherapeutic agent will vary depending on the type of cancer that is going to be treated with the combination of the invention. The skilled person can easily determine which cancer chemotherapeutic agent is more suitable to treat a particular type of cancer.
Also optionally, in step S4, a Glutathione (GSH) depleting agent is provided to the target site in addition to the anti-carcinogenic compound. The GSH depleting agent may be administered by any suitable means, such as orally or intravenously. It is noted that the GSH depleting agent may be provided before or simultaneously to steps S1, S2 and step S3 or a predetermined time after step S1, S2 or S3, preferably at a predetermined time after step S3. The GSH depleting agent provided may be any GSH depleting agent disclosed herein, including in relation to
The term “glutathione depleting agent”, as used herein, refers to a substance that reduces or eliminates glutathione from a cell that has been contacted with that substance. The skilled person is able of determining if a particular molecule is a glutathione depleting agent, for example, by comparing the effect of the particular molecule with the effect of buthionine sulfoximine (BSO), a specific inhibitor of gamma-glutamyl-cysteinyl ligase, using the methodology described for in vitro and in vivo conditions by Terradez P et al, Biochem J 1993, 292 (Pt 2): 477-83. In a particular embodiment, a particular molecule is a glutathione depleting agent if said molecule has at least a 10%, at least a 20%, at least a 30%, at least a 40%, at least a 50%, at least a 60%, at least a 70%, at least a 80%, at least a 90%, a 100% or more of the glutathione-depleting effect of buthionine sulfoximine. Illustrative non-limitative examples of glutathione depleting agents are:
g) A glucocorticoid receptor antagonist, as described by Min, et al., J Mol Med (Berl) 2012, 90: 309-319.
The term “glucocorticoid receptor antagonist” refers to a compound that binds a glucocorticoid receptor and lacks any substantial ability to activate the receptor itself. The term “glucocorticoid receptor antagonist” includes both neutral antagonists and inverse antagonists. A “neutral antagonist” is a compound that blocks the action of the agonist but has no effect on intrinsic or spontaneous receptor activity. An “inverse antagonist” is able to both block the action of the agonist at the receptor and attenuate the constitutive activity of the receptor. The term “antagonist” also includes competitive antagonists, which are drugs that bind to the same site as the natural ligand; noncompetitive antagonists which bind to a different site on the receptor than the natural ligand; reversible antagonists which bind and unbind the receptor at rates determined by receptor-ligand kinetics; and irreversible antagonists which bind permanently to the receptor either by forming a covalent bond to the active site or just by binding so tightly that the rate of dissociation is effectively zero. Non-limitative examples of glucocorticoid receptor antagonists are RU-486 (mifepristone), RU-43044, octahydrophenanthrenes, spirocyclic dihydropyridines, triphenylmethanes and diaryl ethers, chromenes, dibenzyl anilines, dihydroisoquinolines, pyrimidinediones, azadecalins, aryl pyrazolo azadecalins, 11-monoaryl steroids, phenanthrenes, dibenzol [2.2.2]cycloctanes and derivatives, dibenzoclycloheptanes and their derivatives, dibenzyl anilinesulfonamides and their derivatives, dihetero(aryl) pentanol, chromene derivatives, azadecalins, aryl quinolones, 11 ,21-bisaryl steroids and 11-aryl, and 16-hydroxy steroids and the dual antagonist-agonists beclomethasone, betamethasone, budesonide, ciclesonide, flunisolide, fluticasone, mometasone, and triamcinolone. Whether a particular compound is a glucocorticoid receptor antagonist can be determined, for example, by commercial kits, like the Glucocorticoid receptor pathway reporter kit (BPS BIOSCIENCE, SAN DIEGO, CA, USA)
In a particular embodiment, the glutathione depleting agent of the combination of the invention is selected from the group consisting of: a) a Bcl-2 antisense oligodeoxynucleotide; b) an inhibitor of multidrug resistance protein 1; c) an inhibitor of the gamma-glutamyl transpeptidase; d) an inhibitor of cystine uptake; e) disodium glutathione disulfide; f) phenethyl isothiocyanate; g) a glucocorticoid receptor antagonist; h) an anti-IL-6 agent; i) buthionine sulfoximine; j) diethylmaleate; k) NPD926; 1) parthenolide; m) piperlongumine and n) an inhibitor of a protein from the bromodomain and extraterminal domain family, in particular GSK525762A or I-BET762.
In a more particular embodiment the inhibitor of multidrug resistance protein 1 is verapamil, which is a compound having the formula
In a more particular embodiment, the inhibitor of gamma-glutamil transpeptidase is acivicin, which is a compound having the formula
In a more particular embodiment, the inhibitor of cystine uptake is sulfasalazine, which is a compound having the formula
In a more particular embodiment, the glucocorticoid receptor antagonist is RU-486 or mifepristone, which is a compound having the formula
In a more particular embodiment, the anti-IL-6 agent is an inhibitory antibody against IL-6 or an inhibitor of the IL-6 receptor. In an even more particular embodiment, the anti-IL-6 agent is selected from the group consisting of tocilizumab, elsilimomab and siltuximab. The term “tocilizumab” refers to a humanized monoclonal antibody against the IL-6 receptor. The term “elsilimomab” refers to a mouse monoclonal antibody against IL-6. The term “siltuximab” or “CNTO 328” refers to a chimeric monoclonal antibody against IL-6.
In a more particular embodiment, the inhibitor of a protein from the bromodomain and extraterminal domain family is selected from the group consisting of JQ1, GSK525762A and OTX-015. The term “JQ1” refers to a compound of formula
The term “GSK525762A” refers to a compound of formula
The term “OTX-015” refers to a compound of formula
The term “CPI-0610” refers to the compound of reference CAT#: 206117 markered by MedKoo Biosciencies Inc.
In a particular embodiment, the glutathione depleting agent is diethylmaleate, GSK525762A (I-BET762) or piperlongumine.
In step S5, the direct heating is stopped and in step S6 the non-ionizing alternating electric field is stopped. It is noted that steps S5 and S6 may occur simultaneously or the direct heating may be stopped before the non-ionizing alternating electromagnetic field is stopped, such that only the non-ionizing alternating electromagnetic field is applied for a predetermined time after the direct heating is stopped.
It is noted that the order in which the steps are presented in
For example, the non-ionizing alternating electromagnetic field (e.g. at 300 kHz) may be provided at the same time as the anti-cancer composition and the GSH depletor (for example pterostilbene and gemcitabine). The alternating electromagnetic field is applied for two hours, and heating is applied within this two-hour period (for example to heat the target site to a temperature of 52° C. for 10 minutes). In another example, non-ionizing alternating electromagnetic field may be provided first (e.g. at 300 kHz) for a first time period (e.g. 2 hours), and upon expiry of the first time period heating is applied in combination with the anti-cancer composition and/or the GSH depletor (for example pterostilbene with heating to 47° C. for two hours).
In the method, the non-ionizing alternating electromagnetic field may have a frequency of between 10 kHz to 500 kHz, providing a magnetic flux density between 0.1 pT and 1 mT, or between 0.1 pT and 100 or between 100 μT, and 1 mT, and/or the corresponding electric field strength amplitude of between 1 V/cm and 3 V/cm depending on the tissue impedance and may be applied for a time period of between 1 minute and 24 hours.
The direct heating preferably heats the target site to a temperature of at least 42° C., and preferably between 42° C. and 57° C.
The mechanism by which the oscillating magnetic field of the tumour treating field may cause heating of the tissue is through inducing Foucault currents (or “eddy currents”) in the tissue. These currents revolve around the magnetic field lines in the tissue and by the Joule effect could heat the tumour cells. This is due to the conductivity, σ, of the living tissue. The conductivity of tumour tissue increases with increasing frequency of the oscillating magnetic field and is approximately 0.15 siemens/metre at 300 kHz. This conductivity provides the path for microscopic eddy currents which flow in circular paths. The power per unit mass, P, that heats these cells is given by the following equation:
P=π
2
B
2
d
2
f
2/(6. ρ. D)
Where B is the magnetic flux density, d is the depth of tissue over which the magnetic field is provided, f is the field frequency, ρ is the tissue resistivity (inverse to the electrical conductivity) and D is the mass density of the tissue.
The conductivity of tumour tissue can be up to five times higher than the conductivity of healthy tissue and has an approximate value of 0.15 siemens/metre at 100-300 kHz. D for biological tissue is variable (between 900-1050 kg/m3), but can be approximated by that of water, 1000 kg/m3. The highest magnetic flux density of the tumour treating field is 1 mT. The highest frequency is 300 kHz. In the in vitro experiments, the thickness of the culture flask was approximately 1 mm which is the value of d. This gives a value for P of 20 pW/kg. This is an extremely low value. The mechanism of the TT-field is therefore not due to heating. Cell death may be the consequence of charge disruption in the mitochondria. This effect is stronger in tumour tissues due to its higher conductivity, approximately five times higher than the conductivity of healthy cells. The synergetic effect with hyperthermia could be attributable to an increase of the conductivity associated with an increase in the mobility of the charged molecules.
All of the above are fully within the scope of the present disclosure and are considered to form the basis for alternative embodiments in which one or more combinations of the above described features are applied, without limitation to the specific combination disclosed above.
In light of this, there will be many alternatives which implement the teaching of the present disclosure. It is expected that one skilled in the art will be able to modify and adapt the above disclosure to suit its own circumstances and requirements within the scope of the present disclosure, while retaining some or all technical effects of the same, either disclosed or derivable from the above, in light of his common general knowledge in this art. All such equivalents, modifications or adaptations fall within the scope of the present disclosure.
| Number | Date | Country | Kind |
|---|---|---|---|
| 21382115.0 | Feb 2021 | EP | regional |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2022/053424 | 2/11/2022 | WO |
