Power generation device for harvesting energy by fluid-solid triboelectric nanogenerator

Abstract

The present disclosure relates to a power generation device for harvesting energy from the flow of a body fluid flowing through or over the power generation device by fluid-solid triboelectric nanogenerator. The power generation device comprises a solid component on which a surface charge can be induced, at least one electrically conductive component included in or fixed to the solid component, and an output unit for outputting electric power. The at least one electrically conductive component is electrically connected with the output unit. The solid component is configured to be in contact with the body fluid flowing through or over the power generation device by implanting the power generation device into a living organism or by contacting or approaching the power generation device with a living organism.

Description

Technical Field

[0001] This disclosure relates to a power generation device for harvesting energy via a fluid-solid triboelectric nanogenerator. It also relates to a self-powered sensing device including such a power generation device; a system including a self-powered sensing device; and a wearable or implantable medical device. Furthermore, this disclosure relates to the use of the power generation device. Background Technology

[0002] Cardiovascular disease (CVD) is one of the leading causes of death worldwide. According to data provided by the World Health Organization (WHO) in 2022, approximately 18 million deaths worldwide are related to CVD, representing about 32% of all deaths. Unfortunately, due to sedentary lifestyles and an aging population, CVD is increasing around the world and is now one of the leading causes of disability-adjusted life years (DALYs) loss.

[0003] Encouragingly, cardiac electronic devices (CEDs) (such as pacemakers, defibrillators, or ventricular assist devices) have been developed for managing CVD. However, modern implantable or wearable devices that require power to operate have their limitations. In particular, they typically require bulky, short-life batteries and introduce the risk of leakage of their contents.

[0004] Conditions such as atrial fibrillation, congenital heart disease, coronary artery disease, or cardiomyopathy require treatment using CEDs. These CEDs include pacemakers, implantable cardioverter defibrillators (ICDs), cardiac resynchronization therapy (CRT) devices, and left ventricular assist devices (LVADs). Approximately 85% of servicing procedures for these devices are due to battery depletion, and these procedures involve replacing the entire device or main unit (computer / electronics and battery).

[0005] CEDs sometimes even require complete replacement. This poses additional health risks to patients, as such replacements can lead to infections, pain, and hematomas. This means that long-term treatment costs cannot always be kept to a satisfactory level.

[0006] Therefore, there is a need to improve wearable and implantable electric devices, and in particular, to improve wearable and / or implantable sensing systems that address at least one of the aforementioned disadvantages. Summary of the Invention

[0007] One aspect of this disclosure relates to a power generation device for harvesting energy from the flow of bodily fluids passing through or through the device via a fluid-solid triboelectric nanogenerator.

[0008] Triboelectric nanogenerators are energy harvesters that operate based on the triboelectric effect. The triboelectric effect refers to the phenomenon that dielectric materials (electrically insulators, which can be polarized, for example, under electrical stimulation, or spontaneously polarized, for example) and / or their surfaces become charged when in contact with another material of opposite triboelectric polarity. This phenomenon of becoming charged through contact with a charged substance is also called contact electrification. The triboelectric polarity of a surface depends on the material's tendency to lose or gain electrons, thus generating positive or negative charges, respectively.

[0009] When using a solid-to-solid triboelectric generator (Solid-to-solid TENG), two materials in contact move relative to each other due to external mechanical movement, and surfaces with opposite charges periodically transition from a material with higher energy to a material with lower occupied surface state energy. This generates a potential difference—electrostatic induction—between electrodes attached to the back of the materials and connected via an external circuit. Electrostatic equilibrium is maintained by the reciprocating motion of free electrons. This produces an electrical output. The so-called single-electrode (SE) mode of the TENG can have a very simple configuration, in which a single electrode is grounded, and the contact separation or sliding of the triboelectric surfaces is established by a current flowing between the ground and the other electrode.

[0010] The term "fluid-solid triboelectric nanogenerator" (also abbreviated as "Flu-TENG") used in this article refers to a nanogenerator that uses a fluid and a solid as two materials as the triboelectric layer. Similar to traditional solid-solid contact TENGs, when the fluid moves over a solid surface, opposite charges are generated in the two materials.

[0011] The flow of bodily fluids through a power generation device refers to a configuration in which the power generation device itself includes at least one path through which bodily fluids flow.

[0012] A bodily fluid flowing through a power generation device refers to a configuration in which the bodily fluid does not flow into the internal space of the power generation device itself, but rather flows through the power generation device, for example, by flowing along the outer surface of the power generation device.

[0013] The power generation device may include a solid component on which surface charges can be induced. The induction of charges may actually occur on the solid component itself, or on a conductive component disposed on the solid component.

[0014] Specifically, the power generation device may include at least one conductive component. This conductive component may be incorporated into a solid component. In other words, the solid component may be a conductor, or may include one or more conductors. One or more conductive components may be attached to the solid component. Conductive material may be sprayed, applied, or otherwise applied to the solid component.

[0015] The power generation device may include an output unit for outputting electricity. The output unit may be configured to output electricity to a consuming unit. However, the output unit may simply output electricity that can be detected by an internal or external detection unit. The detection unit may be located remotely.

[0016] The at least one conductive component can be electrically connected to the output unit. This enables power output.

[0017] The solid component can be configured to come into contact with bodily fluids flowing through or near the power generation device by implanting the power generation device into a living organism or by contacting or being near the living organism. In other words, once the power generation device is in place, i.e. after it has been implanted into or is in contact with or near the living organism, the solid component can come into contact with bodily fluids flowing through or near the power generation device.

[0018] This could allow the use of bodily fluids (which may be in motion) as one of the two components of a fluid TENG. In this way, energy can be harvested from the moving bodily fluids, such as blood, urine, sweat, filtered blood, lymph, cerebrospinal fluid, serum, bile, plasma, saliva, synovial fluid, menstrual fluid, or tears.

[0019] The power generation device according to this disclosure allows for the output of power to medical devices implanted in or near living organisms. This can conveniently power devices such as cardiac electronics and / or sensors without the need for battery replacements. This may help monitor health conditions, promote longevity, reduce inconvenience, and lower the risks associated with surgical interventions related to maintenance (e.g., replacing medical device batteries). The latter, in particular, can prevent patients from experiencing infection risks, pain, and / or hematomas. Furthermore, long-term treatment costs for patients may be reduced.

[0020] Furthermore, the power generation device according to this disclosure can be very small, thus offering advantages compared to conventional power generation devices used inside or outside living organisms. Additionally, the power generation device according to this disclosure can mitigate the risks associated with the leakage of toxic substances found in conventional power generation devices.

[0021] The described fluid-solid TENG can have advantages over solid TENG, particularly in terms of reduced mechanical wear, as the latter's durability is largely affected by wear, thus impairing long-term performance and stability. Furthermore, the influence of external factors may be less significant, whereas with solid TENG, it may be difficult to guarantee proper contact between the triboelectric layer materials. In contrast, fluids have the ability to adjust their shape, thereby promoting better contact between the two electrodes of the fluid-solid TENG. Therefore, the electrical output of the power generation device according to this disclosure can be improved.

[0022] Solid components may include at least one polymer and / or at least one metal. As mentioned above, the at least one metal may be a conductive component.

[0023] Specifically, solid components may include one or more materials selected from the group consisting of: expanded polytetrafluoroethylene (ePTFE), polyethylene terephthalate, poly(L-lactic acid) (PLLA), poly-2-hydroxyethyl methacrylate graphene oxide (pHEMA / GO), polyethylene glycol graphene oxide (PEG / GO), other polymers (e.g., tubular polymers), silicon, polyurethane, metals (e.g., titanium, aluminum, gold, platinum, nickel, copper and / or stainless steel), and metal alloys (e.g., nickel-titanium, cobalt-chromium alloys, magnesium alloys, brass).

[0024] The solid component may include an inner cavity through which bodily fluids flow. This is an example of a configuration for a power generation device that allows bodily fluids to pass through it.

[0025] Solid components may include a surface (particularly an inner surface) facing the cavity, on which charges can be induced. For this purpose, the surface may include conductive elements or be made of a conductive material.

[0026] For example, the inner surface of a solid component may have an annular shape and extend partially or completely around the inner cavity. This could be a configuration when using a power generation device as part of an artificial graft, etc.

[0027] At least a portion of the solid component may be hollow and configured to allow bodily fluids to flow through it. This is an example of a configuration for a power generation device that allows bodily fluids to pass through it. This hollow configuration, in particular, provides the possibility for bodily fluids to flow into the power generation device and, after obtaining energy from it, flow out of the device.

[0028] The power generation device may include at least partially tubular components. For example, if the power generation device forms part of an artificial blood vessel, the artificial blood vessel may be a tubular component.

[0029] The inner diameter of the at least partially tubular portion can range from 0.1 mm to 40 mm.

[0030] The inner diameter of the at least partially tubular portion can range from 0.5 mm to 30 mm, from 1 mm to 20 mm, from 1.1 mm to 10 mm, from 1.2 mm to 6.0 mm, or from 1.3 mm to 2.0 mm.

[0031] In each of the above cases, the part can be not only partially tubular, but also completely tubular.

[0032] The wall thickness of the at least partially tubular portion can range from 10 micrometers (µm) to 10 mm, or optionally from 15 µm to 1000 µm, from 50 µm to 700 µm, or from 70 µm to 600 µm.

[0033] This disclosure also relates to a power generation device for harvesting energy from the flow of bodily fluids flowing through or passing through the device via a fluid-solid triboelectric nanogenerator. The device may include at least one conductive component configured to contact a solid component, which in turn contacts the bodily fluids flowing through or passing through the device, by implanting the device into a living organism or by contacting or being near a living organism. In other words, the solid component is not necessarily part of the power generation device. For example, natural blood vessels within a living organism can constitute the solid component of the fluid-solid TENG, wherein metal can be sprayed (or otherwise deposited) onto the blood vessels, and the metal particles are the conductive component as described above.

[0034] The power generation device may include an output unit for outputting electricity. The power generation device may be configured to output electricity to a consumption unit. In other cases, the electricity may not be output to the consumption unit, but may be monitored for detection purposes.

[0035] The at least one conductive component can be electrically connected to the output unit.

[0036] In combination with any of the foregoing features (any aspect), the at least one conductive component may be configured to partially or completely wrap around a solid component (e.g., before placing the power generation device at a location for energy harvesting purposes), or the at least one conductive component may partially or completely wrap around a solid component (in some examples this is often the case, while in other examples this is the case once the power generation device is placed at a location for energy harvesting purposes).

[0037] Additionally or alternatively, the at least one conductive component may be configured to be physically and / or chemically bonded to a solid component, or the at least one conductive component may be physically and / or chemically bonded to a solid component (in some examples this is often the case, while in other examples it is only the case once the power generation device is placed in a location for energy harvesting purposes).

[0038] The at least one conductive component may be configured to be brushed, sprayed, deep-coated, sputtered, or bonded to a solid component, or the at least one conductive component may be brushed, sprayed, deep-coated, sputtered, or bonded to a solid component (in some examples this is often the case, while in other examples it is only the case once the power generation device is placed in a location for energy harvesting purposes).

[0039] The at least one conductive component may be configured to be directly or indirectly exposed to bodily fluids flowing through or around the power generation device when the power generation device is implanted in a living organism or when the power generation device is in contact with or near a living organism.

[0040] Direct exposure means that the at least one conductive component is in contact with bodily fluids. Indirect exposure means that the at least one conductive component is not in contact with bodily fluids because something is present between them. However, charge can still be induced due to the passage of bodily fluids.

[0041] The power generation device may include a wire that electrically connects at least one conductive component to the output unit.

[0042] The at least one conductive component may include at least one element selected from the group consisting of: silver, carbon-based materials (e.g., graphite, graphene, or carbon nanotubes), poly(3,4-ethylenedioxythiophene): polystyrene sulfonate (PEDOT:PSS), copper, magnesium, silver nanoparticles, platinum, gold, tantalum, titanium, silicone, iridium, iridium oxide, indium tin oxide, niobium, yttrium barium copper oxide, magnesium diboride, bronze, brass, iron, and tungsten.

[0043] The length of the at least one conductive component can range from 10 nanometers (nm) to 50 centimeters (cm), and optionally from 100 nm to 50 cm, from 1 µm to 50 cm, from 10 µm to 20 cm, from 0.5 cm to 10 cm, or from 1 cm to 9 cm.

[0044] The power generation device may include a plurality of conductive elements configured to be directly or indirectly exposed to bodily fluids flowing through or through the power generation device, and the plurality of conductive elements are electrically connected to an output unit.

[0045] This disclosure also relates to a self-powered sensing device, which includes a power generation device according to this disclosure (including one or more of the features described above).

[0046] The self-powered sensing device according to this disclosure allows for sensing output after the device is implanted in, comes into contact with, or is near a living organism. This enables convenient sensing operations without the need for battery replacements. This can help monitor health conditions, promote longevity, reduce inconvenience, and lower the risks associated with surgical interventions related to maintenance (e.g., replacing batteries in medical devices), as the self-powered sensing device may not require any batteries at all. The latter, in particular, can prevent patients from experiencing infection risks, pain, and / or hematomas. Furthermore, long-term treatment costs for patients may be reduced.

[0047] Furthermore, the self-powered sensing device according to this disclosure can be very small, thus offering advantages over conventional sensing devices used inside or outside living organisms. Additionally, the self-powered sensing device according to this disclosure can mitigate the risks associated with leaks of toxic substances found in conventional sensing devices.

[0048] Specifically, the length of at least one conductive component of the self-powered sensing device can range from 10 nm to 40 cm, from 15 nm to 20 cm, or from 20 nm to 10 cm.

[0049] The self-powered sensing device can be configured to be implanted in, above, or around blood vessels, fistulas, bronchi, intestines, nephrons, ureters, eustachian tubes, and / or fallopian tubes.

[0050] This self-powered sensor can be configured to transmit data to external devices. This functionality can be used to alert patients or healthcare providers, and / or to integrate the self-powered sensor into the Internet of Medical Things (IoMT).

[0051] This self-powered sensing device can be configured to wirelessly transmit data to external devices. This feature can be used to alert patients or healthcare providers, and / or to integrate the self-powered sensing device into the Internet of Medical Technology (IoMT).

[0052] This self-powered sensing device can be configured to perform a function in response to sensing a predetermined signal. This function could be the release of a drug. For example, it could release a predetermined amount of drug, or release a predetermined amount of drug over a period of time.

[0053] This self-powered device can serve as a smart device for diagnosis and / or treatment. For example, it can release medication in response to sensing a predetermined volume. Alternatively, it can release medication to dissolve blood clots whenever a blockage in a vascular graft is sensed.

[0054] This disclosure also relates to a system comprising a self-powered sensing device according to this disclosure, the self-powered sensing device including any or more of the features described above (including any or more features of the power generation device according to this disclosure).

[0055] The system can be configured to measure the potential difference between a first potential measured at a first time point and a second potential measured at a second time point. The first and second potentials can be measured at the same location or at different potentials. The system can be configured to measure more potentials at more time points, either at the same location (relative to at least one of other measurement locations) or at their respective different locations.

[0056] This system can be configured to detect flow obstructions (such as thrombi, biofilms, and encrustations) based on the potential difference between a first and a second potential. In particular, blood flow obstructions, thrombi, biofilms, and / or encrustations can be detected much earlier. Therefore, this system can proactively respond to impending problems before they manifest any symptoms.

[0057] For example, blood flow can be highly dependent on the type of blood vessel and its location within a living organism, as it can vary with pressure differential (ΔP) and is inversely proportional to vascular resistance (R), which comprises the resistance that must be overcome to force blood to flow through the circulatory system. Linking these variables together, blood flow (Q) can be defined by the Hagen–Poiseuille equation, which can also be applied to other types of fluids, as shown below. Q=

[0058] Where r is the radius of the blood vessel, and η is the viscosity of the blood. The length of the vessel is considered. This can also be applied to implanted vascular grafts. Given that fluid-solid TENGs may be sensitive to changes in flow rate—body fluid flow rate may vary with location, and pathological conditions affecting body fluid flow rate (e.g., changes in blood pressure and viscosity) may also affect the obtained triboelectric output—these factors should be considered during the design of fluid-solid TENGs, depending on the intended application.

[0059] The detection based on the potential difference can be based on whether the potential difference is greater than a first preset threshold and / or less than a second preset threshold.

[0060] The system can be configured to measure the potential difference between a first electrode and a second potential measured at a second electrode. The system can be configured, for example, to use a microarray to measure potentials at multiple locations, and can be configured to measure the potential difference between multiple potentials.

[0061] The system can be configured to measure the current, voltage, and / or power density of the current flowing between the first electrode and the second electrode (or between two or more electrodes), or it can be configured to perform multiple measurements at different locations.

[0062] The system can be configured to detect flow obstructions (e.g., thrombi, biofilms, and / or crusts) based on the potential difference between the first and second electrodes.

[0063] The system can be configured to detect flow obstructions (e.g., thrombi, biofilms, and / or crusts) based on whether the potential difference exceeds a first preset threshold and / or falls below a second preset threshold.

[0064] The system can be configured to detect flow obstructions (such as thrombi, biofilms, and / or crusts) based on whether the difference between the potential difference at a first time point and the potential difference at a second time point exceeds a second preset threshold.

[0065] This disclosure also relates to a wearable or implantable medical device comprising a power generation device according to this disclosure (including any one or more of the features described above) and / or a self-powered sensing device according to this disclosure (including any one or more of the features described above).

[0066] Wearable or implantable medical devices may be selected from the following list: catheters, endovascular stents, tubular medical devices, drainage tubes, chest tubes, abdominal drainage tubes, feeding tubes, ventriculoperitoneal shunts, vascular grafts, decellularized blood vessels, autologous grafts, xenografts, allogeneic grafts, collagen-based grafts, decellularized organs, and components of extracorporeal circulation machines (e.g., including tubes or fittings).

[0067] Wearable or implantable medical devices may include a consumable unit. The output unit of a power generation device may be connected to the consumable unit.

[0068] Consumable units can be selected from the following list: sensors, medical electronic devices (e.g., cardiac electronic devices, pacemakers, implantable cardioverter defibrillators, cardiac resynchronization therapy devices, artificial hearts, artificial organs, and left ventricular assist devices).

[0069] The wearable or implantable medical device may be an implantable vascular graft, which includes a tubular body that is included in or serves as a solid component of a power generation device.

[0070] This disclosure also relates to the use of a power generation device (or self-powered sensing device or system) according to this disclosure (including any one or more of the features described above), the power generation device being used to output power and / or as a sensing device by monitoring the power output of a power output unit.

[0071] Monitoring of power output can include determining changes in the flow of bodily fluids over time or between at least two locations, or determining the adsorption of one or more biological components (such as thrombi, biofilms, bacteria, or proteins) along the power generation device.

[0072] A power generation device (or a self-powered sensing device or system) can be used to sense changes in the flow of bodily fluids such as blood, urine, filtered blood, lymph, cerebrospinal fluid, serum, bile, plasma, saliva, synovial fluid, menstrual fluid, or tears.

[0073] Power generation devices (or self-powered sensing devices or systems) can be used to power wearable or implantable electronic medical devices.

[0074] Other advantages and features of this disclosure may be implemented individually or in combination with one or more of the features described above (provided that these features do not contradict each other), and these advantages and features will become apparent in the following description of specific embodiments. Attached Figure Description

[0075] To better understand this disclosure and to illustrate how to implement it, reference will now be made to the accompanying drawings by way of example only, in which: This description is given with reference to the accompanying drawings, in which: Figure 1 Embodiments of a power generation device according to the present disclosure are depicted; Figure 2 A cross-sectional view of a power generation device according to this disclosure is depicted; Figure 3A Depicting as Figure 2The first possible charge generation mechanism of fluid-solid TENG, which is part of a power generation device; Figure 3B Depicting as Figure 2 A second possible charge generation mechanism for fluid-solid TENGs, which is part of a power generation device; Figure 4 A cross-sectional view of a power generation device according to this disclosure is depicted; Figure 5A Depicting as Figure 4 The first possible charge generation mechanism of fluid-solid TENG, which is part of a power generation device; Figure 5B Depicting as Figure 4 A second possible charge generation mechanism for fluid-solid TENGs, which is part of a power generation device.

[0076] Figure 1 An embodiment of the power generation device 1 according to the present disclosure is depicted. In this embodiment, the power generation device 1 is configured to harvest energy from the blood flow of a living organism.

[0077] Figure 1 A natural blood vessel or vascular graft 100 within a living organism is depicted. The power generation device 1 is shown in a state where it has been implanted within the living organism.

[0078] The circled area shows the power generation device 1, which harvests energy from the flow of bodily fluid passing through it via a fluid-solid triboelectric nanogenerator. While in this case, bodily fluid flows through the power generation device 1, in other embodiments, the fluid may alternatively flow over it (e.g., along the outer surface of the device 1).

[0079] Figure 2 It shows Figure 1 The cross-sectional view of the power generation device 1 depicted in the figure shows, in particular, the fluid-solid TENG (TENG stands for triboelectric nanogenerator) setup.

[0080] Body fluid 200 flows through the power generation device 1. In this embodiment, body fluid 200 is blood flowing through a natural blood vessel or blood from the vascular graft 100. However, in other embodiments, body fluid 200 may vary. For example, body fluid may be urine, filtered blood, lymph, cerebrospinal fluid, serum, bile, plasma, saliva, synovial fluid, menstrual fluid, or tears.

[0081] In this embodiment, the body fluid 200 can flow within the natural blood vessel 100 (variant A) or the vascular graft (variant B). In this respect, both variants A and B are based on... Figure 1 and Figure 2 Examples of the content described herein.

[0082] The natural blood vessel 100 or vascular graft 100 is a solid component of the fluid-solid TENG. In the case of the natural blood vessel 100, the solid component is not part of the power generation device 1, but rather part of a living organism. In contrast, in the case of the vascular graft 100, the solid component can be a component of the power generation device 1.

[0083] Surface charge can be sensed on natural blood vessels 100 (variant A) or vascular grafts (variant B).

[0084] Electrodes, acting as conductive elements 10, are (partially or entirely) wrapped around a natural blood vessel 100 or a vascular graft 100. This is in Figure 1 and Figure 2 The text has already been described.

[0085] At once Figure 1 and Figure 2 In one embodiment, the power generation device 1 further includes a power management unit, as an example of an output unit 20 for outputting power. Output unit 20.

[0086] also, Figure 1 and Figure 2 An embodiment includes a wire 30 that electrically connects the conductive component 10 to the output unit 20.

[0087] As from Figure 1 and Figure 2 It becomes apparent that the natural blood vessel 100 (variant A) or the vascular graft 100 (variant B) (as an example of a solid component) comes into contact with the bodily fluid 200 (blood in this example) flowing through the power generation device 1.

[0088] Blood flow causes relative movement between blood components (especially plasma, blood cells, and salts) and the vessel walls or vascular grafts (once implanted in a patient), thus generating friction that causes all related components to become triboelectrically charged. In particular, the membranes of red blood cells (erythrocytes) have unique properties that allow for a high level of triboelectricity.

[0089] In this example, the vascular graft 100 comprises expanded polytetrafluoroethylene (ePTFE). However, in other embodiments, the material may differ. More generally, the vascular graft 100 may include, for example, one or more materials selected from the group consisting of: expanded polytetrafluoroethylene (ePTFE), polyethylene terephthalate, poly(L-lactic acid) (PLLA), poly-2-hydroxyethyl methacrylate graphene oxide (pHEMA / GO), polyethylene glycol graphene oxide (PEG / GO), other polymers (e.g., tubular polymers), silicone, polyurethane, metals (e.g., titanium, aluminum, gold, platinum, nickel, copper, and / or stainless steel), and metal alloys (e.g., nitinol, cobalt-chromium alloys, magnesium alloys, brass).

[0090] In this example, the natural blood vessel 100 or the vascular graft 100 is hollow and includes an inner lumen through which blood flows. The inner surface of the natural blood vessel 100 or the vascular graft 100 faces the inner lumen and can be induced with electrical charge.

[0091] In this case, the electrode, as an example of the conductive component 10, is tubular. However, other shapes (e.g., partially tubular or entirely different shapes) are also possible.

[0092] Figure 3A and Figure 3B Depicting Figure 2 The power generation device 1 is perpendicular to Figure 2 A cross-sectional view with the direction of the cross-section. That is, Figure 3A and Figure 3B A cross-sectional view is shown along a direction perpendicular to the length direction of the natural blood vessel 100 (variant A) or the vascular graft 100 (variant B).

[0093] Figure 3A and Figure 3B Two possible charge generation mechanisms for the fluid-solid TENG are demonstrated. Figure 1 and Figure 2 Part of the power generation device depicted in the image.

[0094] At once Figure 3A In this case, positively charged bodily fluids flow through the power generation device 1. Therefore, an excess of negative charge is induced or pre-charged onto a solid component, which, in the depicted embodiment, may in particular be a natural blood vessel 100 (variant A) or a vascular graft 100 (variant B). This, in turn, means that an excess of positive charge is induced on an electrode, an example of a conductive component 10 forming part of the power generation device 10.

[0095] In comparison, Figure 3BIn this case, negatively charged bodily fluids flow through the power generation device 1. Consequently, a positive charge is induced on a solid component, which, in the depicted embodiment, may in particular be a natural blood vessel 100 (variant A) or a vascular graft 100 (variant B). This, in turn, means that a negative charge is induced on an electrode, an example of a conductive component 10 forming part of the power generation device 10.

[0096] exist Figure 3A and Figure 3B The diagram depicts a general-purpose load 40 as an example of a location to which an output unit or (according to an embodiment) consumption unit is to be connected. For example, wires can be connected to a fluid-solid TENG to harvest energy.

[0097] Figure 4 A cross-sectional view of an embodiment of the power generation device 1 is shown, particularly depicting the fluid-solid TENG (TENG stands for triboelectric nanogenerator) setup.

[0098] Figure 4 An embodiment is a power generation device 1, wherein the solid component 110 is a vascular graft 110 made of a synthetic material containing metal particles, which serve as an example of a conductive component.

[0099] Figure 5A and Figure 5B Two possible charge generation mechanisms for the fluid-solid TENG are demonstrated. Figure 4 Part of the power generation device 1 depicted in the text.

[0100] At once Figure 5A In this case, positively charged bodily fluids flow through the power generation device 1. As a result, a negative charge is induced on the solid component 110.

[0101] In comparison, Figure 5B In this case, negatively charged bodily fluids flow through the power generation device 1. As a result, a positive charge is induced on the solid component 110.

[0102] Figure 5A and Figure 5B The diagram depicts a general-purpose load 40 as an example of a location to which an output unit or (according to an embodiment) consumption unit is to be connected. For example, wires can be connected to a fluid-solid TENG to harvest energy.

[0103] Example Exemplary power generation devices were fabricated to demonstrate the generation of electrical energy from a living source by utilizing the flow of bodily fluids (particularly blood in arteries and vascular grafts) in natural blood vessels and (biological) materials.

[0104] Fluid-solid TENGs were developed using synthetic vascular grafts (particularly commercially available ePTFE or lab-produced pHEMA / GO) and natural arteries as the solid phase. Different fluids were tested, namely phosphate-buffered saline (PBS), plasma, and blood. Silver, carbon, and PEDOT:PSS conductive inks and copper foil strips were tested as electrodes, targeting their stability (washing test and SEM), efficiency (electrical output), and biocompatibility (for fibroblasts (HFF-1)) in the solid phase.

[0105] Exemplary assembly of the conductive ink electrode on ePTFE was performed by brush coating, as a stable coating was observed and no penetration into the interior of the vascular graft was observed. Silver exhibited higher stability with pHEMA / GO vascular grafts and arteries. The performance of the fluid-solid TENG was evaluated based on its saturation by charging 1 nF and 100 nF capacitors. A higher output (23.6 V) was obtained with plasma as the fluid phase, and the result with PBS was closer to that with blood (14.2 V) compared to PBS (17.3 V). The performance of the fluid-solid TENG was observed to depend on the flow rate of the body fluid. For example, an increase in flow rate of 100 mL / min was associated with an increase in output of approximately 10 V. Different electrodes were tested, for example, an output of 17.3 V was obtained using silver, 12.9 V using carbon, and 10.4 V using PEDOT:PSS. The output was observed to depend linearly on the electrode length, with an increase of 30 V observed when the silver electrode was increased from 0.5 cm to 10 cm. The analyzed solid phases exhibited triboelectric properties, with at least 10.5 V obtained using ePTFE, 14.5 V using a pHEMA / GO vascular graft, and 8 V using an artery. These results are affected by the material wall thickness; increasing the wall thickness and inner diameter both decrease the output. Finally, the potential of Flu-TENG as a stenosis sensor was demonstrated, as the flow disturbance caused by 30% stenosis in the ePTFE vascular graft resulted in an 8 V perturbation in the electrical output. Therefore, the change in the electrical signal can be correlated with the degree of stenosis, thus enabling its detection.

[0106] Exemplary expanded polytetrafluoroethylene (ePTFE) vascular grafts for use in peripheral bypass surgery have been manufactured. Specifically, the exemplary vascular grafts have different inner diameters (ID) and wall thicknesses (WT), such as 1.5 mm ID and 100 µm WT; 4 mm ID and 500 µm WT; 4.5 mm ID and 75 µm WT; and 6 mm ID and 152 µm WT.

[0107] In addition, a vascular graft (with a 4 mm ID and 1 mm WT) made of poly(2-hydroxyethyl methacrylate) (an FDA-approved hydrogel) and graphene oxide (pHEMA / GO) was used to observe the triboelectric effect. For preparative purposes, 2-hydroxyethyl methacrylate (HEMA) monomers were in situ polymerized in the presence of 1% (m / v) GO (prepared via a modified Hummer method using graphene oxide) and 3% (v / v) tetraethylene glycol dimethacrylate (TEGDMA) as a crosslinking agent, by adding a 1:1 mixture of 1.5% (v / v) 40% ammonium persulfate (APS) and 15% sodium metabisulfite (SMB). 3D tubing was produced using plastic tube molds with diameters of 6 mm and 4 mm, and an inner glass rod. After the hydrogel was allowed to stand overnight, it was removed from the mold and rinsed with distilled water.

[0108] In addition, studies have been conducted on using natural coronary arteries as solid components.

[0109] For conductive components, different conductive inks were investigated, such as silver (VFP ink technology, SE-001) and carbon (Elantas, Bectron). GP 9553 and poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS, Heraeus, Clevios™ S V4 STAB, 81098168) were applied to blood vessels or grafts by brushing. All conductive inks were attached to copper wires to allow connection to the acquisition setup. For synthetic vascular grafts, the inks were cured at 130 °C for 10 minutes to achieve optimal conductivity, as recommended by the ink supplier; for natural blood vessels, they were air-dried at room temperature for 30 minutes to avoid damage to the vessels due to high temperatures. In addition to the conductive inks, copper foil strips were tested as electrodes. The copper foil strips were wrapped in different solid phases. For silver conductive inks, the effects of different electrode lengths (0.5, 1, 2, 4, 6, 8, and 10 cm) and different electrode designs on the achieved triboelectric output were tested.

[0110] The experimental data obtained are as follows (see Table 1):

[0111] Table 1 Figures 6 to 13B Experimental evidence corresponding to Table 1 is shown, obtained from studies of various embodiments of the fluid-solid TENG according to this disclosure. Figures 6 to 13A The measured voltage output over time is shown. Figure 13B The current output based on the resistance is shown.

[0112] Figure 6 Experimental evidence of charging a 1 nF capacitor using a fluid-solid TENG is presented, with different fluids flowing through the TENG. Three different fluids were used as the corresponding fluid stages of the TENG: phosphate-buffered saline (PBS), plasma, and blood. The following three corresponding curves are shown: these curves illustrate the change of the measured voltage over time.

[0113] Figure 7 Experimental evidence of charging a 1 nF capacitor using a fluid-solid TENG is presented, where the flow density of the fluid flowing through the fluid-solid TENG varies. Specifically, a flow density of 161 mL / min was compared with a flow density of 268 mL / min. This is an indicator of how charging capacity changes with perturbed versus undisturbed flow in the blood vessel. The tested fluid-solid TENG consisted of a solid phase (composed of ePTFE with an inner diameter of 6 mm and a wall thickness of 152 μm) and a 2 cm long silver electrode. Observations showed that the output increased with increasing flow rate.

[0114] Figure 8Experimental evidence of charging a 1 nF capacitor using fluid-solid TENGs with different electrode lengths is presented. The following electrode lengths were tested: 0.5 cm, 1 cm, 2 cm, 4 cm, 6 cm, 8 cm, and 10 cm. The tested fluid-solid TENGs comprised a solid phase (composed of ePTFE with an inner diameter of 1.5 mm and a wall thickness of 100 μm) and employed a PBS fluid phase (with a flow density of 161 mL / min).

[0115] Figure 9 Experimental evidence is presented showing the charging of a 1 nF capacitor using fluid-solid TENGs with different types of electrodes (different electrode materials). Specifically, silver electrodes, carbon electrodes, and PEDOT:PSS electrodes were used. The fluid-solid TENGs tested comprised a solid phase (composed of ePTFE with an inner diameter of 1.5 mm and a wall thickness of 100 μm) and a PBS fluid phase (with a flow density of 161 mL / min).

[0116] Figure 10 Experimental evidence is presented for charging a 1 nF capacitor using fluid-solid TENGs with varying solid-phase wall thicknesses. Specifically, a wall thickness of 75 μm (4.5 mm inner diameter) is compared to a wall thickness of 500 μm (4 mm inner diameter). The fluid phase was PBS (with a flow density of 161 mL / min), and the electrode was a 2 cm long silver electrode. Observations of the results show that higher output is achieved when the solid-phase wall thickness decreases.

[0117] Figure 11 Experimental evidence of charging a 1 nF capacitor using fluid-solid TENGs with different inner diameters is presented. Specifically, an inner diameter of 1.5 mm (100 μm wall thickness) is compared with an inner diameter of 6 mm (152 μm wall thickness). The tested fluid-solid TENGs consisted of a solid phase (composed of ePTFE) and a fluid phase of PBS (with a flow density of 161 mL / min). The attached figure shows that a smaller diameter results in a higher output.

[0118] Figure 12 Experimental evidence is presented for charging a 1 nF capacitor using fluid-solid TENGs with different solid phases. The solid phases tested included ePTFE (4 mm inner diameter, 500 μm wall thickness), PHEMA / GO (4 mm inner diameter, 1 mm wall thickness), and natural artery (umbilical cord). The tested fluid-solid TENGs had a PBS fluid phase (with a flow density of 161 mL / min) and a 2 cm long silver electrode.

[0119] Figure 13AExperimental evidence of charging a 1 nF capacitor using a fluid-solid TENG is presented, comparing undisturbed and disturbed flow (the flow disturbance being 30% narrower in the solid phase, resulting in a corresponding increase in resistance). The tested fluid-solid TENG consisted of a solid phase (composed of ePTFE with an inner diameter of 4 mm and a wall thickness of 500 μm); a PBS fluid phase (with a flow density of 161 mL / min); and a 2 cm long silver electrode.

[0120] Figure 13B The measured values ​​are shown. Figure 13A The relevant fluid-solid TENG, based on the current of the resistance.

[0121] By comparison Figure 13A and Figure 13B The electrical signals acquired during the test showed an increase in current output across all tested resistors at a 30% stenosis in the solid phase. Furthermore, the voltage output also increased. Therefore, the fluid-solid TENG is well-suited for detecting stenosis in vascular grafts or natural vessels, as the corresponding electrical signals are excellent indicators of the occlusion and its degree.

[0122] In this document, when it is mentioned that a structural component (e.g., a system, device, etc.) is configured to perform a certain operation, it can also be understood as expressing that the system or device is performing that operation (e.g., mentioning that a component is configured to perform sensing can also be understood as disclosing that the component is actually performing sensing, etc.).

[0123] It will be apparent to those skilled in the art that various modifications and variations can be made to the disclosed apparatus and systems without departing from the scope of this disclosure. Other aspects of this disclosure will become apparent to those skilled in the art upon consideration of the specification disclosed herein and practice with the features. The specification and examples are intended to be considered illustrative only. Many other changes and modifications are possible and should be understood to fall within the framework of this disclosure.

Claims

1. A power generation device for harvesting energy from the flow of bodily fluids passing through or through the device via a fluid-solid triboelectric nanogenerator. The power generation device includes: Solid components, on which surface charges can be induced. At least one conductive component, said at least one conductive component being included in or fixed to said solid component, and Output unit, the output unit is used to output power, wherein The at least one conductive component is electrically connected to the output unit, and The solid component is configured to come into contact with bodily fluids flowing through or near the power generation device by implanting the power generation device into a living organism or by contacting or being close to the living organism.

2. The power generation device according to claim 1, wherein, The solid component comprises at least one polymer and / or at least one metal; The solid component may optionally include one or more materials selected from the group consisting of: expanded polytetrafluoroethylene (ePTFE), polyethylene terephthalate, poly(L-lactic acid) (PLLA), poly-2-hydroxyethyl methacrylate graphene oxide (pHEMA / GO), polyethylene glycol graphene oxide (PEG / GO), other polymers (e.g., tubular polymers), silicon, polyurethane, metals, and metal alloys, wherein the metals are, for example, titanium, aluminum, gold, platinum, nickel, copper, and / or stainless steel, and the metal alloys are, for example, nitinol, cobalt-chromium alloys, magnesium alloys, and brass.

3. The power generation device according to claim 1 or 2, wherein, The solid component includes an inner cavity and an inner surface facing the inner cavity, the inner cavity being for allowing bodily fluids to flow through it, and the inner surface being capable of inducing electrical charges.

4. The power generation device according to any one of the preceding claims, wherein, At least a portion of the solid component is hollow and configured to allow bodily fluids to pass through it.

5. The power generation device according to claim 4, comprising: At least part of it is tubular.

6. The power generation device according to claim 5, wherein, The inner diameter of the at least partially tubular portion ranges from 0.1 mm to 40 mm, and optionally from 0.5 mm to 30 mm, from 1 mm to 20 mm, from 1.2 mm to 10 mm, or from 1.5 mm to 6.0 mm.

7. The power generation device according to claim 4 or 5, wherein, The wall thickness of the at least partially tubular portion ranges from 10 µm to 10 mm, and optionally from 15 µm to 1000 µm, from 50 µm to 700 µm, or from 70 µm to 600 µm.

8. A power generation device for harvesting energy from the flow of bodily fluids passing through or through the device via a fluid-solid triboelectric nanogenerator. The power generation device includes: At least one conductive component, the at least one conductive component being configured to contact a solid component by means of implanting the power generation device into a living organism or by means of contacting or proximity of the power generation device to the living organism, the solid component being in contact with bodily fluid flowing through or through the power generation device; and Output unit, the output unit is used to output electricity. The at least one conductive component is electrically connected to the output unit.

9. The power generation device according to any one of the preceding claims, wherein, The at least one conductive component is configured to partially or completely wrap around the solid component and / or be physically or chemically bonded to the solid component, for example, the at least one conductive component is configured to be brushed, sprayed, deep-coated, sputtered, or bonded to the solid component.

10. The power generation device according to any one of the preceding claims, wherein, The at least one conductive component is configured to be directly or indirectly exposed to the bodily fluid flowing through or passing through the power generation device when the power generation device is implanted into a living organism or when the power generation device is brought into contact with or near the living organism.

11. The power generation device according to any one of the preceding claims, comprising a conductor, wherein, The wire electrically connects the at least one conductive component to the output unit.

12. The power generation device according to any one of the preceding claims, wherein, The at least one conductive component comprises at least one element selected from the group consisting of: silver, carbon-based materials, poly(3,4-ethylenedioxythiophene):polystyrene sulfonate (PEDOT:PSS), copper, magnesium, silver nanoparticles, platinum, gold, tantalum, titanium, silicone, iridium, iridium oxide, indium tin oxide, niobium, yttrium barium copper oxide and magnesium diboride, bronze, brass, aluminum, iron and tungsten, wherein the carbon-based material is, for example, graphite, graphene or carbon nanotubes.

13. The power generation device according to any one of the preceding claims, wherein, The length of the at least one conductive component ranges from 10 nm to 50 cm, and optionally from 100 nm to 50 cm, 1 µm to 50 cm, 10 µm to 20 cm, 0.5 cm to 10 cm, or 1 cm to 9 cm.

14. The power generation device according to any one of the preceding claims, comprising a plurality of conductive elements configured to be directly or indirectly exposed to the bodily fluid flowing through or through the power generation device, and the plurality of conductive elements being electrically connected to the output unit.

15. A self-powered sensing device, comprising: The power generation device according to any one of the preceding claims.

16. The self-powered sensing device according to claim 15, wherein the self-powered sensing device is configured to be implanted in, above or around a blood vessel, fistula, bronchus, intestine, nephron, ureter, Eustachian tube and / or fallopian tube.

17. The self-powered sensing device according to claim 15 or 16, wherein the self-powered sensing device is configured to transmit data to an external device, optionally wirelessly.

18. The self-powered sensing device according to any one of claims 15 to 17, wherein the self-powered sensing device is configured to perform a function in response to sensing a predetermined signal, optionally, the function being the release of a drug.

19. A system comprising a self-powered sensing device according to any one of claims 15 to 18, wherein, The system is configured to measure the potential difference between a first potential measured at a first time point and a second potential measured at a second time point, and The system is configured to detect flow obstructions based on the potential difference, such as thrombi, biofilms, and crusts. Optionally, the system is configured to detect flow obstructions based on whether the potential difference exceeds a first preset threshold.

20. A system comprising a self-powered sensing device according to any one of claims 15 to 19, wherein, The system is configured to measure the potential difference between a first electrode and a second potential measured at a second electrode, and / or to measure the current, voltage, or power density of the current flowing between the first and second electrodes. The system is configured to detect flow obstructions based on the potential difference, such as thrombi, biofilms, and crusts; optionally, the system is configured to detect the flow obstructions based on whether the potential difference exceeds a first preset threshold, and / or based on whether the difference between the potential difference at a first time point and the potential difference at a second time point exceeds a second preset threshold.

21. A wearable or implantable medical device, comprising a power generation device according to any one of claims 1 to 14 or a self-powered sensing device according to any one of claims 15 to 20. The wearable or implantable medical device is selected from the following list: catheters, endovascular stents, tubular medical devices, drainage tubes, chest tubes, abdominal drainage tubes, feeding tubes, ventriculoperitoneal shunts, vascular grafts, decellularized blood vessels, autologous grafts, xenografts, allogeneic grafts, collagen-based grafts, decellularized organs, and components of extracorporeal circulation machines, such as tubing.

22. The wearable or implantable medical device of claim 21, comprising a consumable unit, wherein, The output unit is connected to the consumption unit, and The consumable units are selected from the following list: sensors, medical electronic devices, such as cardiac electronic devices, pacemakers, implantable cardioverter defibrillators, cardiac resynchronization therapy devices, artificial hearts, artificial organs, and left ventricular assist devices.

23. The wearable or implantable medical device according to claim 22, wherein, The wearable or implantable medical device is an implantable vascular graft, which includes a tubular body, and the tubular body is the solid component.

24. Use of the power generation device according to any one of claims 1 to 14, wherein the power generation device is used to output electricity and / or to act as a sensing device by monitoring the electricity output by the power output unit.

25. The use of the power generation device according to claim 24, wherein, Monitoring the power output includes: determining changes in the flow of the body fluid over time or changes in the flow of the body fluid between at least two locations, or determining the adsorption of one or more biological components along the power generation device, such as thrombi, biofilms, bacteria, or proteins.

26. Use of the power generation device according to claim 24 or 25, wherein the power generation device is used to sense changes in the flow of the body fluid, such as blood, urine, filtered blood, lymph, cerebrospinal fluid, serum, bile, plasma, saliva, synovial fluid, menstrual fluid, or tears.

27. Use of the power generation device according to any one of claims 1 to 14, wherein the power generation device is used to power a wearable or implantable electronic medical device.

Images