Fluid electrical sensors

Abstract

An electrical sensor for sensing the electromagnetic properties of a fluid being processed in a dialysis machine or similar medical device may include a probe made of an electronic fabric material for contact with the fluid. The electronic fabric probe may include one or more conductors embedded in a non-conductive fabric layer. The electronic fabric probe is housed in a housing that establishes a flow path relative to the probe to establish fluid contact between the processed fluid and the conductors. The conductors may apply or sense a current and / or voltage with respect to the fluid. A portion of the electronic fabric probe may be disposed outside the housing to provide electronic communication with the outside of the housing.

Description

Background Technology

[0001] Hemodialysis is a medical procedure used to treat patients with kidney failure, kidney problems, or other related conditions where the kidneys cannot adequately remove impurities and waste products from the patient's blood. During hemodialysis, a dialysis system or machine removes blood from the patient and guides it through a filtration device called a dialyzer, which filters and purifies the blood before returning it to the patient. The filtration process is achieved by guiding a liquid solution (usually called dialysate) through the dialyzer, where it passes through a membrane and separates from the blood in the dialyzer, allowing waste products to be drawn into or diffuse into the dialysate. To facilitate treatment for different patients with different conditions, the composition of the dialysate can be adjusted or modified during dialysis, for example, by introducing different additives to adjust its properties.

[0002] To facilitate the preparation and adjustment of dialysate solutions, various sensors and control devices are integrated into dialysis machines to monitor the preparation process and the composition of the dialysate solution. By using these sensors and control devices, the dialysis machine can be designed to automatically adjust during dialysis treatment, or for healthcare professionals to make necessary adjustments while monitoring the sensors and control devices. Therefore, sensors and control devices can play a crucial role in dialysis treatment. However, because the dialysis process inevitably involves human biological material, sensors and control devices must be integrated into the dialysis machine in a manner that isolates them or cleans and / or sterilizes them. This disclosure relates to supplementing and improving the operation and functionality of sensors and control devices associated with dialysis machines or similar medical devices. Summary of the Invention

[0003] This disclosure provides an electrical or electromechanical sensor for analyzing a process fluid in a dialysis machine or similar medical device by measuring or sensing certain electromagnetic properties associated with the fluid. To communicate directly with the fluid, the electrical or electromechanical sensor may utilize an electronic fabric probe with conductive properties, made of a flexible, non-conductive fabric layer having one or more electrical conductors exposed on the fabric layer. The conductors may be attached to the fabric layer by spinning, sewing, combing, weaving, or other suitable methods. This type of electronic fabric may also be referred to as electronic textile or smart fabric. The electronic fabric probe may be cut or trimmed and positioned within a non-conductive housing defining a fluid chamber. The process fluid may be directed into the fluid chamber to electrically contact the exposed conductors of the electronic fabric probe. Thus, voltage and / or current can be applied to the process fluid in the fluid chamber using the conductors in the electronic fabric probe. To establish electrical communication with the conductors, a portion of the electronic fabric probe may extend outside the housing. In one embodiment, the housing may be formed of molded plastic or the like and may be easily removable to allow for the removal of the electronic fabric probe.

[0004] A potential advantage is that this disclosure provides an electrical sensor that can detect electromagnetic properties, such as electromagnetic field characteristics, associated with the processing fluid in a dialysis machine or similar device, by using conductive electronic fabric. The electronic fabric probe can be cut from a large strip of electronic fabric material, thus providing unique manufacturing benefits associated with this disclosure. Another potential advantage is that, since the housing can be made of low-cost molded plastic and is easily disassembled, the electrical sensor can be easily removed from the dialysis machine and disposed of as a whole, or the electronic fabric probe can be removed from the housing and replaced. This advantage is readily understood considering the electrical sensor's exposure to potentially biohazardous processing fluids.

[0005] On the other hand, this disclosure describes various uses of electronic fabric probes to measure different properties of fluids in a fluid loop, such as flow rate or fluid pressure. Electrode conductors embedded in a non-conductive fabric layer can be configured to measure these fluid properties based on the electrical characteristics of the electronic fabric probe associated with the conductor configuration. Alternatively, the conductor configuration can provide identification or verification features that transmit information about the electronic fabric probe, for example, to ensure that the electronic fabric probe is a correct probe or is correctly installed. Furthermore, the electronic fabric probe can be configured to shield the electrode conductors from electromagnetic fields, etc. The advantage of these aspects of this disclosure is the use of inexpensive and disposable electronic fabric for various fluid measurements and sensor types. Moreover, the electronic fabric probe can be used as a backup or diagnostic sensor to assist other sensors in a system. These and other advantages will become apparent from the following detailed description and accompanying drawings. Attached Figure Description

[0006] Figure 1 This is a front view schematic diagram of a dialysis system that uses dialysate fluid to process blood removed from a patient and includes electrical sensors for analyzing the fluid used during dialysis.

[0007] Figure 2 This is an exploded view of an embodiment of an electrical sensor for a dialysis system, which utilizes a four-conductor electronic fabric probe disposed in a housing with a crossflow configuration.

[0008] Figure 3 yes Figure 2 A partial cross-sectional perspective view of the assembly of an embodiment shows fluid flow through an electronic fabric probe and an electrical sensor.

[0009] Figure 4 yes Figure 2 A detailed perspective view of the area indicated in the image shows structural details of an embodiment of the electronic fabric probe.

[0010] Figure 5This is an exploded view of another embodiment of an electrical sensor, which utilizes a dual-conductor electronic fabric probe disposed in a housing having a flow-through structure.

[0011] Figure 6 yes Figure 5 A perspective assembly diagram of an embodiment is shown, illustrating fluid flow through an electrical sensor and with enclosed elements indicated by dashed lines.

[0012] Figure 7 This is a partial cross-sectional perspective view of another embodiment of the electrical sensor, which utilizes multiple electronic fabric probes to analyze different aspects of the fluid used during dialysis.

[0013] Figure 8 This is a partial cross-sectional perspective view of another embodiment of the electrical sensor, which has at least five electrical conductors embedded in an electronic fabric probe to measure the flow rate of fluid passing through the electrical sensor.

[0014] Figure 9 This is a perspective view of another embodiment of an electrical sensor, in which an electronic fabric probe is arranged in a tubular flow configuration to measure fluid pressure via a capacitance associated with the probe.

[0015] Figure 10 It is along Figure 9 The cross-sectional view taken by line 10-10 shows an electrical sensor with an electronic fabric probe set under normal fluid pressure.

[0016] Figure 11 It is similar to Figure 10 A cross-sectional view showing an electronic fabric probe set under increased or excessive fluid pressure.

[0017] Figure 12 This is a perspective view of an embodiment of an electrical sensor, which configures an electronic fabric probe to measure fluid pressure via an inductance associated with the electrical sensor.

[0018] Figure 13 This is a perspective assembly diagram of an embodiment of an electrical sensor including an electronic fabric probe having multiple electrical conductors configured to provide visual indication for identification or verification of the electronic fabric probe.

[0019] Figure 14 This is a perspective assembly diagram of an embodiment of an electronic fabric probe, configured to mate with an electrical connector and including dedicated electrode conductors to identify or verify the mated electrical connector.

[0020] Figure 15 yes Figure 14 A detailed view of the area indicated in the image shows another dedicated electrical conductor set up as an antenna to transmit radio signals to identify the electronic fabric probe.

[0021] Figure 16 This is a perspective view of another embodiment of an electronic fabric probe, which has an active first conductor group and a passive second conductor group for providing electromagnetic shielding for an electrical sensor.

[0022] Figure 17 yes Figure 16 The perspective view of the folded and assembled electronic fabric probe allows the passive second conductor group to shield the active first conductor group.

[0023] Figure 18 This is a schematic diagram of a circuit using an electronic sensor that enables an electronic fabric probe to detect filters in a fluid circuit. Detailed Implementation

[0024] Referring now to the accompanying drawings, in which the same reference numerals denote the same elements, Figure 1 The illustration shows a specific embodiment of a dialysis machine 100, illustrating a medical system for performing hemodialysis treatment on a patient 102. It should be noted that while various aspects of this disclosure are described with respect to hemodialysis treatment, these aspects may have applications beyond hemodialysis treatment and are not intended to be specifically limited to hemodialysis unless explicitly stated otherwise, nor are the claims so. Furthermore, the illustrated dialysis machine can be used for home use or for portability outside of a medical clinic; however, unless explicitly stated herein, various aspects of this disclosure are applicable to other configurations of dialysis treatment, and the claims are not intended to be so limiting. The dialysis machine 100 may be equipped with a dialyzer 110 in which blood filtration is performed. The dialyzer 110 may be a cross-flow dialyzer, in which blood flowing in one direction is separated from dialysate flowing in the opposite direction by a semipermeable membrane. During the dialysis process, solutes, fluids, and impurities in the blood can diffuse or transfer across the membrane to the dialysate to be drawn from the dialyzer 110. In various embodiments, dialyzer 110 may be a single-use device or may be configured for multiple uses.

[0025] To guide blood from patient 102 to dialyzer 110, catheter 112 is inserted into the patient and can be connected to dialyzer 100 via tubing or removal line 114. Catheter 112 may be temporarily inserted for the procedure or may be surgically implanted into patient 102. To maintain blood flow from patient 102 to dialyzer 110, pump 116, such as a rotary peristaltic pump, may be operatively associated with the dialyzer and can be positioned along removal line 114 to supply pressure to the line guiding or supplementing blood flow in the appropriate direction. Filtered blood from dialyzer 110 is returned to patient 102 via return line 118.

[0026] To supply dialysate during dialysis treatment, the dialysis machine 100 can be operatively associated with a dialysate system 120 configured to prepare and regulate the dialysate solution. In one embodiment, the dialysate system 120 may be an adsorbent system in which the dialysate is reformulated and recycled by the dialysis machine 100 without significant waste. However, in other embodiments, the dialysis machine may be a more conventional single-pass system in which used dialysate must be stored in a suitable container for final disposal. To introduce fresh dialysate into the dialyzer 110, the dialyzer may be configured to be in fluid communication with the dialysate system 120 via a dialysate supply line 122, which may be a flexible hose or a tube made of a suitable medical material. A peristaltic pump 124 may be disposed in the line along with the dialysate supply line 122, applying appropriate pressure to guide the dialysate solution through the dialyzer 110. After the backflowing blood has passed through dialyzer 110 to be treated, the dialysate is returned to dialyzer 110 via dialysate return line 126, which can be associated with a third peristaltic pump 128 to maintain the flow of the dialysate solution.

[0027] To facilitate the recirculation and remediation of used dialysate, the dialysate solution is guided to the adsorbent cartridge 130 via dialysate return line 126, where the fluid is cleaned and purified. The adsorbent cartridge 130 may be a disposable unit made of multiple layers or segments formed from different elements and compounds, which capture and remove impurities from the dialysate solution that were introduced from the blood during the dialysis process. The impurities remain in the adsorbent cartridge 130, while the filtered dialysate is returned to the dialysis machine 100 via the adsorbent return line 132. The advantage of the adsorbent system is that it allows for the recirculation of a large volume of dialysate solution, including the purified reverse osmosis water initially used as dialysate, while providing a convenient way to handle biological impurities removed from the patient's blood via the dialyzer 110. However, in various embodiments, the adsorbent return line 132 may be in fluid communication with a reverse osmosis water source 134, which can replenish the water content of the recirculated solution if necessary.

[0028] To further restore the solution returned from the adsorbent cartridge 130, the dialysate system 120 may include a cartridge or dialysate bag 136 disposed within the dialysis machine and containing various additives and chemicals. The dialysate bag 136 may also include tubing or flow channels for directing the recirculated solution into contact with the additives used for blending and may be further partitioned to separate the additives. To facilitate the adsorption of additives into the recirculated solution and to prevent the patient's blood from cooling during dialysis, the dialysate bag 136 may be operatively associated with a heater 138. The added dose may be measured and intended for use in a single dialysis treatment session, or in other embodiments, the added dose may be added to the recirculated solution via a suitable metering device. In single-use embodiments, the dialysate bag 136 may be removed from the dialysis machine and replaced after use. In addition to the dialysate bag 136, the dialysate system 120 may include other sources of compounds and fluid solutions for preparing the dialysate and may be associated with meters and detectors to check the presence, quality level, composition, and formulation of blood in the dialysate, and may include a degasser, etc. Freshly prepared dialysate is reintroduced to the dialyzer via dialysate supply line 122. To provide power for operating peristaltic pumps 124, 128 and heater 138, as well as other equipment, the dialyzer 100 may be operatively associated with a power source 139 (e.g., a plug for an electrical outlet or, in other embodiments, a rechargeable battery pack).

[0029] To monitor and control the dialysis process, an electronic or computerized control unit, module, or controller 140 may be operatively associated with the dialysis machine 100. The controller 140 is adapted to monitor various operating parameters and responsively adjust various variables and functions affecting the dialysis system 120 and other systems of the dialysis machine 100. The controller 140 may include a microprocessor 142, an application-specific integrated circuit (ASIC), or other suitable circuitry, and may have memory 144 or other data storage capabilities on a computer-readable medium. The microprocessor 142 and memory 144 may be configured to store, retrieve, and execute programmed instructions for the dialysate formation and recirculation processes, and to respond adaptively to changes in the process. To enable technicians or operators to communicate with the dialysis machine, the controller 140 may be operatively associated with a human-machine interface 146, such as a liquid crystal display device that may include touchscreen capabilities. The human-machine interface 146 may display visual information about the dialysis process and the operating status of the dialysis machine 100, and may receive input from the operator via tactile capabilities. The controller 140 may be further associated with a physical control panel 148, which includes switches, knobs, keyboards, etc., through which the operator can start and adjust the dialysis process.

[0030] To monitor and analyze the composition, parameters, and properties of the fluid solution processed by the dialysate system 120, the dialyzer 100 may include various sensors, particularly electrical sensors, configured to be in fluid communication with the system. The sensors may be electrically or electronically actuated and may operate on electromagnetic principles to analyze and measure information about the fluid that is important to the dialysis process. Measured parameters may include conductivity, temperature, flow rate, pH, and other characteristics. For example, to analyze and determine the composition and quality of the recirculated dialysate before directing it to the dialyzer 110, the dialyzer 100 may include a supply sensor 150 located upstream of the dialyzer in the dialysate supply line 122. Additionally, to receive and determine the quality and composition of the used dialysate returned from the dialyzer 110 after treating the patient's blood, a return sensor 152 may be located downstream of the dialyzer in the dialysate return line 126. The supply and return sensors 150 and 152 may also be electrically connected to the controller 140 to send and receive information between components. Communication can be established by sending and receiving non-transitory analog or digital signals via a communication bus (such as a wire, optical waveguide, etc.) provided through the dialyzer 100. Additional electrical sensors can be incorporated at other locations within the dialysate system 120 to monitor other fluid properties.

[0031] conductivity sensor

[0032] To analyze dialysate from a dialysis machine or other processing fluids in similar medical devices, electrical sensors can be positioned in direct fluid contact with the target fluid and can include electrical or electronic components configured to assess the electrical or magnetic properties of the fluid. For example, in one embodiment, the electrical sensor can be a conductivity sensor that measures the conductivity of the target fluid. Most liquids are capable of conducting or transferring electric current to some extent. Charge is carried by electrolytes or ions, including cations (positive) and anions (negative) present in the fluid. The number of ions in the fluid, and therefore the fluid's ability to conduct or resist electric current, depends on several factors, including the fluid's composition, temperature, flow rate, and volume. If factors such as volume and temperature are known and described, the measurable conductivity of the fluid can be used to infer the unknown composition of the fluid.

[0033] To measure the electrical conductivity of a fluid, an electrical sensor is configured to apply a current or voltage to a volume of fluid between two predetermined points or locations. The fluid's resistivity, which is the mathematical inverse of its conductivity, causes a decrease or reduction in the voltage and / or current between the two points due to the electrical flow through it. A suitable meter can measure the decrease in those parameters reflecting the fluid's resistivity, thereby establishing the fluid's conductivity through a mathematical relationship. The physical and electrical coupling between the electrical sensor and the fluid occurs in a device or cell called a conductivity cell, which includes electrodes for applying and sensing voltage and / or current.

[0034] Reference Figure 2 and Figure 3 An embodiment of an electrical sensor 200 is shown, configured to establish fluid communication with a processing fluid of a dialysis machine or similar medical device, and includes electrical components such as conductive elements arranged to physically contact the fluid and thus function as a conductivity battery. Specifically, the electrical sensor 200 includes a probe 202 made of an electronic fabric material having one or more conductive electrodes embedded therein, the probe 202 being housed in a non-conductive housing or casing 204 to establish a flow path across the electronic fabric probe 202. Electronic fabrics or electronic textiles are a class of materials used in applications similar to conventional fabrics and textiles, in which electronic components are disposed within a fabric-like or sheet-like material having non-conductive properties. Examples include wearable electronics. Electronic fabrics are characterized by their flexibility, and their sheet-like structure allows them to cover and conform to surfaces. According to one aspect of this disclosure, the electronic fabric probe 202 can be cut or trimmed from a larger strip of electronic fabric material for its specific application in the electrical sensor, thereby facilitating probe manufacturability. For example, various sizes and shapes can be cut from the same electronic fabric strip.

[0035] exist Figure 2 and 4 In the illustrated embodiment, the electronic fabric probe 202 includes a non-conductive fabric layer 210, which may have a planar polygonal shape depicting a rectangular outline or peripheral edge 212. The polygonal shape also provides a first side edge 214 and parallel, spaced-apart second side edges 216 extending perpendicular to the centerline 217 of the fabric layer 210. The fabric layer 210 also has a flexible sheet-like characteristic or property and may consist of individual fibers 218 or threads of natural or synthetic materials, which have been interlocked together, for example, by spinning, weaving, sewing, combing, bonding, knitting, pressing, etc. Alternatively, the non-conductive fabric layer 210 may be made of a flexible thin plastic film. In one embodiment, the non-conductive material for the fabric layer may be made of polyethylene terephthalate (PET) mesh. The fabric layer 210 may have a certain degree of fluid permeability or porosity to facilitate its interaction with the processing fluid of the medical device. The thickness and permeability of the sheet fabric layer 210 can be selected based on the application and fluid flow encountered.

[0036] To provide electrodes for the electronic fabric probe 202, one or more conductors 220, and up to any suitable number of conductors, can be disposed on the fabric layer 210. In the illustrated embodiment, the conductors 220 can be made of a thin strip of conductive material woven, sewn, or otherwise embedded in the non-conductive fabric layer 210 such that at least a portion of the conductor is exposed along the surface of the fabric layer. More specifically, the conductors 220 can be long, thin rectangular lines disposed on the fabric layer to facilitate their electromagnetic effect. Suitable materials for the conductors 220 include stainless steel, aluminum, gold, copper, etc., and the conductors 220 can be stamped from thin metal sheets or foils; however, in other embodiments, the conductors can be formed as thin wire gauges. Figure 4 As shown, in one embodiment, the conductor can be secured to the fabric layer 210 by random fibers extending across the width of the conductor.

[0037] Various types of conductivity sensors are available and can include any suitable number of conductors for performing the selected measurement. For example, in Figure 2 In the illustrated embodiment, the electronic fabric probe 202 can be configured as a four-electrode device and may include a first conductor 222, a second conductor 224, a third conductor 226, and a fourth conductor 228. The first, second, third, and fourth conductors 222, 224, 226, and 228 extend longitudinally between a first side edge 214 and a second side edge 216 of a non-conductive fabric layer and are arranged parallel to each other and spaced apart from each other about a centerline 217. Furthermore, the first conductor 222 and the second conductor 224 may be extended outwards towards the peripheral edge 212 about the centerline 217 at a given first distance 230, while the third conductor 226 and the fourth conductor 228 are extended inwards towards the first and second conductors and spaced apart by a second distance 232 less than the first distance. Since the conductors 220 are embedded in the fabric layer 210 by sewing, weaving, etc., the first distance 230 and the second distance 232 are generally maintainable. The terminal ends of the four conductors along the first side edge 214 may form a corresponding plurality of leads or terminals 236 for the electronic fabric probe 202.

[0038] In order to accommodate the electronic fabric probe 202, Figure 2The housing 204 shown can be constructed as a two-piece structure having a first housing portion 240 and a second housing portion 242 that, when assembled together, can form a closed fluid chamber 244. The first housing portion 240 can be a flat planar structure formed in an oblong or elliptical shape that forms an elliptical profile 250. Protruding from one side of the elliptical profile 250 can be a connector tongue 252, the utility of which will be described more fully below. A small recess 254 is provided in the surface of the flat first housing portion 240 that can extend along the connector tongue 252 toward the opposite edge of the elliptical profile 250. The width of the recess 254 can generally correspond to the width of the fabric layer 210 measured perpendicular to the centerline 217. Therefore, in this embodiment, when the first housing portion is assembled to the second housing portion 242, the electronic fabric probe 202 can be placed adjacent to the planar surface of the first housing portion 240 in the recess 254. When assembled in this way, the first side edge 214 of the fabric layer 210 can be aligned along the connector tongue 252, where the terminals 236 of the conductor 220 can be exposed to the outside of the housing 204.

[0039] To form the fluid chamber 244, the second housing portion 242 can be formed as a hollow dome 260 extending upward from an elliptical base 262 corresponding to the elliptical profile 250 of the lower housing portion 240. The dome 260 can be depicted below as a hollow cavity generally corresponding to the fluid chamber 244. The cross-sectional area and / or volume of the fluid chamber 244 can be predetermined by the shape of the dome 260, which is advantageous for reasons explained below. For connecting the electrical sensor 200 to a tube or hose of the dialysate system, the second housing portion 242 includes an upwardly extending fluid inlet 264 and a corresponding fluid outlet 266, which can be configured as a cylindrical hose fitting. The connection can be established by press fitting, hose clamping, etc. The fluid inlet 264 and fluid outlet 266 are parallel to each other and spaced apart from each other by a third distance 268 toward opposite ends of the elliptical base 262, which can be greater than the first or second distance 230, 232 associated with the fabric layer 210. The first housing portion 240 and the second housing portion 242 can be made of any suitable non-conductive material, such as molded polycarbonate. The first housing portion 240 and the second housing portion 242 can be connected together in a snap-fit ​​relationship by clips or the like, so that the housing 404 can be easily assembled and disassembled.

[0040] To establish electronic communication with the conductor 220 on the electronic fabric probe 202 when it is housed in the assembled housing 204, the electrical sensor 200 can be operatively associated with an attachable electrical connector 270. The electrical connector 270 can be in the form of a pin header having a plurality of conductive leads or pins 272 disposed in and protruding from the insulating housing or shield 274. The electrical connector may further include a slot 276 disposed in the shield 274 opposite to the side protruding from the pins 272, allowing the connector to receive and attach to a connector tongue 252 extending from the lower housing cover 240. Thus, a portion of the pins 272 can make electrical contact with the terminals 236 of the conductor 220 along a first side edge 214 of the fabric layer 210. When the electrical sensor 200 is disposed in a dialysis machine or similar medical device, the electrical connector 270 can mate with a corresponding socket in the device to establish electrical communication between the electrical sensor 200 and the controller of the dialysis machine or similar device.

[0041] You can refer to this. Figure 3 The flow of the processed fluid through the electrical sensor 200 and the resulting conductivity measurement are described. Specifically, the separated regions of the fluid chamber 244 can be further defined as an inlet region 280 corresponding to the fluid inlet 264 and facing one end of the elongated housing 204, and an exit region 282 corresponding to the fluid outlet 266 and facing the opposite end of the housing. The electronic fabric probe 202 adjacent to the lower first housing portion 240 is exposed to the fluid chamber 244, with its upper surface facing the fluid inlet 264 and the fluid outlet 266. Fluid flowing inward into the inlet region 280 and perpendicular to the lower housing portion 240 will be correspondingly horizontally redirected along the fluid flow path 284 to the exit region 282 located at the opposite end of the elongated housing 204. Furthermore, the flow path 284 is generally perpendicular to and passes through each of the conductors 220 embedded in the electronic fabric probe 202, with each conductor traversing the flow path. Preferably, since the electronic fabric probe 202 is disposed in a recess 254 formed in the lower first housing portion 240, the probe's position is maintained when fluid is guided between the fluid inlet 264 and the fluid outlet 266. Furthermore, since the conductors 220 are sewn or woven into the fabric layer, their relative positions with respect to each other are substantially fixed at predetermined first distances 230 and second distances 232. The exposure of the conductors to the fabric layer and the associated fluid permeability facilitate the electrical connection between the conductors and the processing fluid.

[0042] In a four-electrode conductivity cell, the two external electrodes corresponding to the first conductor 222 and the second conductor 224 can be designated as excitation electrodes. The excitation electrodes are coupled to a power source to apply a voltage or current between the first conductor 222 and the second conductor 224, causing current to be conducted through the fluid in the internal chamber 244. The power source can provide alternating current (AC) or direct current (DC). Since the processed fluid is typically an imperfect conductor, the fluid will cause a voltage drop between the first conductor 222 and the second conductor 224. The value of the voltage drop corresponds to the composition of the fluid, such as the presence or absence of ions, impurities, etc. To measure the voltage drop, the two internal electrodes corresponding to the third conductor 226 and the fourth conductor 228 can be designated as sensing electrodes or grounding protection. The sensing electrodes can be coupled to a suitable instrument such as an ammeter or ohmmeter, or preferably to a voltmeter that senses the voltage drop between at least the third conductor 226 and the fourth conductor 228. The instrument can then be coupled to or as part of a controller as described above to perform the following calculations. According to Ohm's law, the measured voltage drop can be converted into the resistance provided by the fluid between the sensing electrodes:

[0043] (Formula 1) Ohm's Law: V = I / R

[0044] Where V is the voltage drop in volts;

[0045] I is the current measured in amperes or milliamperes; and

[0046] R is the resistance measured in ohms or milliohms.

[0047] Since the second distance 232 between the third conductor 226 and the fourth conductor 228 (i.e., the sensing electrode) is predetermined by the setting of the electronic fabric probe 202, the calculated resistance in ohms between the third and fourth conductors can be converted into the resistivity of the fluid. Resistivity is an inherent property of fluids, which quantifies their resistance to current and is typically expressed in ohms × centimeters (Ω × cm). By calculating the measured and calculated resistance in ohms and the resistance in cm of the internal chamber 244... 2 The resistivity can be approximated by multiplying the predetermined cross-sectional area A in units and dividing that value by L (the second distance 232) in cm:

[0048] (Formula 2) ρ=R×A / L

[0049] Since conductivity is the mathematical reciprocal of resistivity, the conductivity of the fluid flowing in the electrical sensor 200 can be easily determined. Once the conductivity of the process fluid is calculated, it can be compared with empirically predetermined values ​​to determine the composition or components of the process fluid, which provides discernible information about the dialysis process and instructions on how to regulate it. The relationship between the above formula and the properties of the process fluid may not be precisely linear or directly proportional; however, calibration or estimation of the calculated and determined values ​​may be necessary.

[0050] According to an advantageous embodiment, all or part of the electrical sensor 200 may be disposable. Specifically, since the housing 204 is connected to the fluid circuit of the dialysis machine via a hose, the electrical sensor 200 can be easily removed from the dialysis machine during the post-use cleaning process. Furthermore, because the housing 204 can be easily disassembled into separate first housing portion 240 and second housing portion 242, the electronic fabric probe 202 can be removed and discarded after use. The first and second housing portions 240, 242 can be sterilized and reused with a newly installed electronic fabric probe 202, or the entire electrical sensor can be discarded. Since the electrical sensor 200 needs to come into contact with the dialysate and other processing fluids, the disposable nature of the sensor, whether entirely or partially disposable, improves its utility in medical and biological applications such as dialysis therapy.

[0051] Although Figure 2 and Figure 4 The illustrated embodiment of the electronic fabric probe has a four-electrode configuration, but other probe configurations are possible, such as two-electrode and three-electrode embodiments. Furthermore, configurations other than the cross-flow configuration are also possible. (See reference...) Figure 5 and Figure 6 The diagram illustrates a dual-electrode flow-through configuration for an electrical sensor 300 to analyze fluids in a dialysis machine or similar medical device. The electrical sensor 300 includes an electronic fabric probe 302, which can be housed within a two-piece non-conductive housing 304 configured to guide the processing fluid through the fabric probe. The electronic fabric probe 302 can be structurally similar to the probe described above and can include a flexible planar fabric layer 310 in which multiple conductors 320 are disposed. To allow fluid to permeate from a first surface 312 through the fabric layer 302 to a second surface 314, the fabric layer 310 can be relatively porous or made of loosely woven, knitted, or braided fibers. Furthermore, in this embodiment, the fabric layer 310 can have a tongue-shaped profile including curved peripheral edges 316 and square or rectangular extensions 318.

[0052] For use as electrodes, the electronic fabric probe 302 may include a plurality of conductors 320, including a first conductor 322 and a second conductor 324 embedded in a fabric layer 310. The first conductor 322 and the second conductor 324 may be relatively thin and elongated strips of conductive material, and may extend parallel and spaced apart from the curved peripheral edge 316 across the longitudinal length of the fabric layer 310 to a rectangular extension 318. Terminals 336 may be formed at the locations where the first and second conductors 322, 324 terminate at the edges of the rectangular extension 318.

[0053] To accommodate the electronic fabric sensor 302 within the flow-through configuration, the housing 304 is a two-piece structure comprising a first or lower housing portion 340 and a second or upper housing portion 342, which can be assembled together to define a fluid chamber 344. In the illustrated embodiment, the lower housing portion 340 and the upper housing portion 342 may each have a corresponding hemispherical dome 346, 348 that defines a corresponding hemispherical cavity. However, it should be noted that terms such as “lower,” “upper,” “lower,” and “upper” are for reference only and should not be construed as limiting the claims unless explicitly stated otherwise. The hemispherical domes 346, 348 may have the same overall dimensions. When assembled together, the first and second hemispherical domes 346, 348 provide a spherical shape for the chamber 344. The lower and upper hemispherical domes 346, 348 may also include corresponding circular bases 350, 352 with corresponding diameters, which engage as flanges when the lower and upper housing portions 342, 344 are assembled. A flat planar connector extension 354, corresponding to a rectangular extension 318 of the electronic fabric conductor 302, may extend vertically from the circular base 350 of the lower housing portion 340.

[0054] When the electrical connector 300 is assembled, the electronic fabric conductor 302 is suspended in a spherical chamber 344, wherein a first surface 312 points towards a lower hemispherical dome 346 and a second surface 314 points upward towards an upper hemispherical dome 348. The curved peripheral edge 316 of the electronic fabric conductor 302 may be clamped between the first and second circular bases 350, 352. To guide fluid through the spherical chamber 344 and across the electronic fabric conductor 302, the lower housing portion 340 may include a downward-pointing fluid inlet 364 and the upper portion 342 may include an upward-pointing fluid outlet 364. The oppositely positioned fluid inlet 364 and fluid outlet 366 depict a fluid flow path 368 similar to an axis positioned across the spherical fluid chamber 344. Processing fluid introduced into the electrical sensor 300 through the fluid inlet 364 must permeate and traverse the electronic fabric sensor 302 to reach the fluid outlet 366. If power is applied to the first conductor 322, designated as the excitation electrode, current will be conducted through fluid across the electronic fabric probe 302 to the second conductor 324, which serves as the sensing electrode. To establish electrical communication with the first and second conductors 322, 324 to apply and sense voltage and / or current, an electrical connector 370, including a plurality of conductive pins 372, can be attached to a connector extension 354 of the lower housing portion 340.

[0055] Flow sensor

[0056] In addition to measuring the conductivity of the fluid being processed, the aforementioned types of electrical sensors can also be configured to measure other parameters and properties of fluids processed by medical devices such as dialysis machines. (See reference...) Figure 7 An embodiment of an electrical sensor 400 with multiple electronic fabric probes 402 is shown, the electronic fabric probes 402 being configured to measure flow rate in addition to conductivity. The multiple electronic fabric probes 402 are housed in a non-conductive housing 404, which defines an internal fluid chamber 406 in which the probes are suspended. The housing 404 is generally drum-shaped, so the fluid chamber 406 depicts a raised cylinder in which the electronic fabric probes 402 are vertically arranged. To establish a flow configuration for the electrical sensor 400, the housing 404 may have a downward fluid inlet 410 and an oppositely oriented upward fluid outlet 412, which depict a flow path 414 through the probes 402 and across the fluid chamber 406. A portion of the electronic fabric probe 402 protrudes radially outward from one side of the housing 404 for connection to an associated device.

[0057] The first electronic fabric probe 420, positioned at the lowest point of the fluid chamber 406, can measure the conductivity of the processed fluid and may have any of the aforementioned configurations. The second, third, and fourth electronic fabric probes 422, 424, and 426 can be configured to determine the flow rate through the fluid chamber 406 by sensing temperature differences in the fluid. Specifically, the third electronic fabric probe 424 may be a heating probe and may include one or more heating conductors 430 embedded in a non-conductive fabric layer 432 of the third electronic fabric probe in the form of a wire or thread. The heating conductors 430 may have sufficient resistance to heat the third electronic fabric probe 424 when current is applied. The heating conductors 430 can transfer the generated heat to the fluid flowing through the third electronic fabric probe 424. The second and fourth electronic fabric probes 422 and 426, positioned above and below the third electronic fabric probe 424, can be configured as thermal sensing probes. For example, the second electronic fabric probe 422 may include a first sensing conductor 440 embedded in a corresponding fabric layer 442, the first sensing conductor 440 being formed as a closed loop for introducing and extracting fluid chamber 406. The resistance associated with the first sensing conductor 440 may be proportionally temperature-dependent and change according to increases and decreases in ambient temperature. The fourth electronic fabric probe 426 may include a second sensing conductor 444 with a similar arrangement embedded in a corresponding fourth fabric layer 446.

[0058] In operation, as the process fluid from fluid inlet 410 flows along flow path 414 and permeates through the second electronic fabric conductor 422, an instrument operatively associated with the first sensing conductor 440 can determine its resistance by measuring the voltage drop across the first sensing conductor. Next, the process fluid permeates the third electronic fabric probe 424, where a heating conductor 430 can transfer the generated heat to the fluid flowing through it. The second sensing conductor 444, disposed in the fourth electronic fabric probe 426, can also be associated with an instrument that determines the resistance of the second sensing conductor by measuring the associated voltage drop. The resistance measurements between the first sensing conductor 440 and the second sensing conductor 444 can be compared to determine the temperature difference between the second electronic fabric probe 422 and the fourth electronic fabric probe 426. If the thermal energy input through the heating conductor 430 is known, the flow rate of the process fluid through the fluid chamber 406 can be readily determined. In yet another embodiment, the electrical sensor can measure other mass and parameters, such as temperature.

[0059] Reference Figure 8Another embodiment of an electrical sensor 500 is shown, configured to measure the conductivity and flow rate of a processed fluid in a medical device, etc., using an electronic fabric probe 502 partially contained in a probe housing 504. The shape and construction of the electronic fabric probe 502 and the probe housing 504 can be similar to those described above. Figure 2 and Figure 3 The described fabric probe 202 and housing 204 can also be complementaryly joined or supported by each other in a similar manner. Thus, the electronic fabric probe 502 may include a non-conductive fabric layer 510, which is thin and planar in shape and made of natural or synthetic fabric or interlocking fiber cloth, or in other embodiments, of a plastic film. The non-conductive fabric layer 510 is flexible and adaptable, and can be fitted or conformed to different shapes or folded onto itself. The fabric layer 510 may be rectangular, including elongated side edges 512 extending between a shorter front edge 514 and a rear edge 516. For reference purposes, a centerline 517 of the rectangular non-conductive fabric layer 510 is disposed between the side edges 512 and perpendicular to the front edge 514 and the rear edge 516.

[0060] For use as electrodes to generate electricity, the electronic fabric probe 500 may include one or more electrode conductors 520 disposed on a fabric layer 502. As previously described, the electrode conductors 520 may be elongated, thin strips or bands of conductive material sewn, woven, or otherwise embedded in the non-conductive fabric layer 510, such that the conductors are partially exposed along the surface of the electronic fabric probe 500 for electrical contact with other elements. However, in other embodiments, the electrode conductors 520 may be made of guide wires, or may be formed by depositing, spraying, or adhering powdered or liquid conductive material to the non-conductive fabric layer. The electrode conductors 520 may be made of any suitable conductive material, including stainless steel, aluminum, gold, and copper, and are preferably thin enough to avoid significantly increasing rigidity to the flexible non-conductive fabric layer 510.

[0061] In the illustrated embodiment where the electrical sensor 500 measures conductivity and flow rate, the plurality of electrode conductors 520 may have at least five (5) conductors, including a first conductor 522 and a second conductor 524 disposed on the opposite side of the fabric centerline 517 toward any of the longer edges 500. The first conductor 522 and the second conductor 524 may be spaced apart from each other by a first distance 526 indicated by an arrow. The plurality of electrode conductors 520 may also include a third conductor 530, a fourth conductor 532, and a fifth conductor 534 disposed between the first conductor 522 and the second conductor 524. The five electrode conductors 520 extend across the non-conductive fabric layer 510 from the front edge 514 to the rear edge 516 in an arrangement parallel to each other and parallel to the side edge 512, at which the leading ends of the conductors 520 may form leads or terminals 536. The five electrode conductors 520 may be different and separated from each other to maintain electrical isolation. In this regard, the third conductor 526, the fourth conductor 527 and the fifth conductor 528 may be evenly spaced apart from each other by a second distance 538, wherein the fourth conductor 532 is arranged approximately along the center line 517 and the third and fourth conductors 530, 534 are offset toward the side edge 512 and the corresponding first and second conductors 522, 524.

[0062] In the illustrated embodiment, the first and second conductors 522, 524 can be designated as the first and second excitation electrodes, respectively, while the third, fourth, and fifth conductors 530, 532, 534 can be designated as the first, second, and third sensing electrodes, respectively. When the electrical sensor 500 mates with an electrical connector and is connected to a medical device, etc., such as... Figure 1 When the dialysis machine 100 is operatively associated with the electrical system of the controller 140, the first and second excitation electrodes 522, 524 can be electrically connected to a power source supplying voltage and / or current. The supplied power can be alternating current (AC) or direct current (DC), and current can flow or conduct between the first and second excitation electrodes 522, 524 when the electronic fabric probe 502 is suspended in the fluid. To measure the voltage drop between the first and second excitation electrodes 522, 524, the first, second, and third sensing electrodes 530, 532, 534 can be electrically connected to a suitable instrument. As described above, the voltage drop measured between the sensing electrodes 530, 532, 534 can be converted to the resistance of the fluid using Ohm's law, and the reciprocal of this resistance can be used to determine the fluid conductivity. Therefore, the electrical sensor 500 is associated with... Figure 2 and Figure 3 The implementation examples are similar to those for measuring electrical conductivity.

[0063] To support and position the electronic fabric probe 502 relative to the fluid to be measured, the probe housing 504 can be a two-piece structure having a first housing portion 540 and a second housing portion 542, which define a closed fluid chamber 544 when assembled together. The first housing portion 540 is a lower portion having a flattened elliptical shape with an outwardly projecting connector tongue 552 above which the electronic fabric probe 502 is positioned. To provide the fluid chamber 544, the second housing portion 542 is an upper portion having a hollow dome construction, including an upwardly extending dome 560 rising from an elliptical base 562 that matches the correspondingly formed first housing portion 540. The first housing portion 540 and the second housing portion 542 can be made of any suitable non-conductive material, including polycarbonate.

[0064] To guide fluid into the probe housing 504 and into contact with the electronic fabric probe 502, the second housing portion 542 may have a fluid inlet 564 extending upward from the dome 560 and a corresponding fluid outlet 566. The fluid inlet 564 and fluid outlet 566 may be cylindrical tubes or hooked hoses and are parallel to each other, located at opposite ends of the elliptical base 562, spaced apart by a third distance 568. The fluid inlet 564 thus guides fluid into the entry region 580 of the fluid chamber 544, while the fluid outlet 564 guides fluid from the oppositely positioned exit region 582. Therefore, this configuration defines a crossflow arrangement for the flow path 584, wherein fluid enters the fluid chamber 544 perpendicularly to the lower first housing portion 540, is vertically redirected to pass over the electronic fabric probe 502 supported on the first housing portion, and is then redirected to exit the fluid chamber 544. The dimension of the third distance 568 between the entry region 580 and the exit region 582 can be larger than the first distance 526 and the second distance 538 defined between the electrode conductors 520, so that the flow path perpendicularly crosses all conductors. While the illustrated flow path 584 through the flow chamber 544 is U-shaped, in other embodiments, the fluid inlet 564 and the fluid outlet 566 can be axially aligned such that the flow path 584 passes straight through the fluid chamber 544 and across the electronic fabric probe. In other embodiments, the flow path 584 may have other configurations or orientations.

[0065] Assuming the fluid has a uniform conductivity, since the second distance 538 between the first sensing electrode 530 and the second sensing electrode 532, and the second distance 538 between the second sensing electrode 534 and the third sensing electrode 536, are equal, the measured voltage drops between those second distances 538 should also be equal. To measure the flow of fluid in the fluid chamber 544, a tracer or pellet can be introduced via a pellet inlet port 586 located upstream of the inlet region 580, for example, possibly in or upstream of the fluid inlet 564. The tracer pellet 588 can be a bubble, fluid, or flowing material that may have similar viscosity and density characteristics to the fluid being measured but different electrical properties (including different conductivity). As the tracer pellet 588 is guided along the flow path 584 near the first sensing electrode 530 and the second sensing electrode 532, the voltage drops and associated conductivity measured by these electrodes will change accordingly. Shortly afterward, as the tracer pellet 588 passes through the second and third sensing electrodes 532, 534, the voltage drop and conductivity will similarly change, while the voltage drop and conductivity between the first and second sensing electrodes can be reverted to the voltage drop and conductivity of the processed fluid. The time difference between the pellet tracer 588 passing through the first, second, and third sensing electrodes 530, 532, 534 can be recorded and converted into the fluid flow rate in the fluid chamber 544 (in millimeters per second or similar units). In other words, the three equidistant sensing electrodes 530, 532, 534 can measure the travel time of the pellet tracer 588 through the electronic fabric probe 502, which can correspond to the flow rate of the fluid carrying the pellet tracer. Therefore, this embodiment of the electrical sensor 500 can measure both fluid conductivity and fluid flow rate.

[0066] In one embodiment, the five-conductor electronic fabric probe 502 can provide self-diagnostic features due to the arrangement of the electrode conductors. Specifically, if the second distance 538 between the first sensing electrode 530, the second sensing electrode 532, and the third sensing electrode 534 is the same, then theoretically they should sense the same conductivity or voltage drop between the three sensing electrodes if the fluid flowing through them has a consistent conductivity. Therefore, if the voltage or conductivity measured between the first and second sensing electrodes 530, 532 differs from the measurement made between the second and third sensing electrodes 532, 534 beyond an acceptable tolerance, this can indicate a problem with the electrical sensor 500. The pellet inlet port 586 can be used to introduce fluid with a known conductivity for this diagnostic purpose.

[0067] Although this embodiment utilizes a series of three sensing electrodes to measure the difference in conductivity, it will be understood that in other embodiments, additional sensing electrodes may be used to perform multiple measurements at various locations on the electronic fabric probe. It should also be understood that the electronic fabric probe can be housed in significantly different housings, thereby providing different flow paths for the fluid of interest.

[0068] Fluid pressure or proximity sensor

[0069] In another aspect of this disclosure, the electrical sensor including the electronic fabric probe can also measure properties other than fluid conductivity, such as fluid pressure or its ability to deform or displace the flexible electronic fabric probe relative to a reference. More specifically, changing the proximity of the electronic fabric probe relative to a reference by altering the force or pressure applied to the probe can result in a change in measurable electrical properties. Therefore, the measured properties can be correlated back to changes in fluid pressure, which can indicate another action or property of the medical device. The variable electrical properties can be capacitance or inductance associated with the electronic fabric probe.

[0070] For example, refer to Figure 9 , Figure 10 and Figure 11 An embodiment of an electrical sensor 600 configured as a tubular flow-through element is shown. The electrical sensor 600 measures the electrical characteristics of an electronic fabric probe 602, which changes size in response to fluid pressure within the electronic fabric probe 602. The electronic fabric probe 602 may be a hollow tubular structure defining an internal fluid chamber 604 for receiving the fluid to be analyzed. To support the electronic fabric probe 602 and guide fluid into it, the electrical sensor 600 may include a rigid support 606 that maintains the tubular shape of the electronic fabric probe 602, thereby defining a longitudinal axis 608 extending between opposite ends. The support 606 may include a first end cap 610 and a second end cap 612 disposed at opposite axial ends of the electrical sensor 600. The first and second end caps 610, 612 may be formed as cylindrical hollow tubes, each defining an axial opening 614 to receive or discharge fluid flowing through the electrical sensor 600. However, in other embodiments, one of the first or second end caps 610, 612 may lack the opening 614, making the electrical sensor 600 effectively a blind end. The first end cap 610 and the second end cap 612 may include a radially raised lip or edge 616 located at the end opposite to the opening 614. The first end cap 610 and the second end cap 612 are preferably made of a non-conductive rigid material, such as polycarbonate plastic.

[0071] To interconnect the axially spaced first and second end caps 610, 612, the tubular electronic fabric probe 602 may have a length corresponding to the axial distance between the first and second end caps. The electronic fabric probe 602 may include a non-conductive fabric layer 620 made of a thin, flexible or resilient material formed as a tubular sleeve surrounding a fluid chamber 604. Suitable materials for the non-conductive fabric layer include woven or spun fabrics, or more preferably synthetic sheets or films. In a preferred embodiment, the non-conductive fabric layer 620 may be made of or include an elastic material to provide elasticity and resilience, and may be fluid-impermeable to retain fluid within the flow chamber 604. The non-conductive fabric layer 620 may be initially formed as a thin planar sheet wound and sealed around an axis 606 to form the tubular electronic fabric probe 602. A first elastic ring 622 and a second elastic ring 624 may be disposed at opposite axial ends. When mounted on the first and second end caps 610, 612, the first and second resilient rings 622, 624 can be received on the respective edges 616 of the end caps 610, 612 to secure the electronic fabric probe 602 in place. The diameters of the first resilient ring 622 and the second resilient ring 624 may be slightly smaller than the edges 616, such that they are elastically compressed around the edges to further secure the electronic fabric probe 602 in place.

[0072] To conduct or sense electricity in the electronic fabric probe 602, a plurality of electrode conductors 630 may be attached to the interior of the non-conductive fabric layer 620. Specifically, the electrode conductors 630 may be formed as longitudinal strips, tapes, or filaments of conductive material extending parallel to the axis 606. Preferably, the electrode conductors 630 may extend at least co-linearly between the first and second elastic rings 622, 624. Furthermore, the electrode conductors 630 may be arranged in opposite radial groups 632 and 634 along the interior of the non-conductive fabric layer 620. Thus, the first conductor group 632 and the second conductor group 634 are physically and electrically separated from each other by the fluid chamber 604. Each of the first conductor group 632 and the second conductor group 634 corresponds to a different radial or symmetrical half of the electronic fabric probe 602.

[0073] In one embodiment, for electrical communication with a plurality of electrode conductors 630, the tail ends of the electrode conductors 630 disposed near the resilient rings 622, 624 can contact corresponding contact pads 636 disposed on the exterior of the first and second end caps 610, 612. The contact pads 636 may be made of a conductive material plated to the first and second end caps 610, 612 near the edges 616 and may extend axially a short distance away from the edges, such that they are partially exposed beyond the first and second resilient rings 622, 624. Thus, the contact pads 636 provide an accessible area and provide contacts or connectors that can be used to connect the electrical sensor 600 to a medical device, in which electrical connections can be established between the electrode conductors 630 disposed within the non-conductive fabric layer 620. Furthermore, one contact pad 636 may be associated with an electrode conductor 630 of a first conductor group 632, and a second contact pad 636 may be associated with a conductor of a second conductor group 634, thus allowing the first and second conductor groups to be electrically connected to separate portions of the circuitry associated with the medical device.

[0074] By suspending the electronic fabric probe 602 between the first end cap 610 and the second end cap 612 of the rigid support 604, the aforementioned arrangement enables the electrical sensor 600 to respond to changes in the fluid pressure of the fluid passing through the sensor. Specifically, arranging the electrode conductors 630 into a first conductor group 632 and a second conductor group 634 allows the electronic fabric probe 602 to measure pressure changes based on corresponding changes in the electrical characteristics of the electrical sensor, for example, based on the capacitance generated between the plurality of electrode conductors 630 in the first conductor group 632 and the plurality of electrode conductors in the second conductor group 634. Since the electrode conductors 630 in the first conductor group 632 and the second conductor group 634 are arranged opposite each other, and if the inner diameter of the electronic fabric probe 602 is small enough, an electromagnetic field and a resulting capacitive charge can be established between the first conductor group and the second conductor group when a current is applied. For example, a circuit such as direct current (DC) can be used via the contact pad 636 on the rigid support 604 to cause a current to be applied to the electrode conductors of the first conductor group 632 and the second conductor group 634. Because the first conductor group 632 and the second conductor group 634 are electrically separated by the fluid chamber 604 and any fluid contained therein, the first conductor group 632 and the second conductor group 634 can operate similarly to opposite plates or terminals of a capacitor and can maintain a charge between them. For example, the first conductor group 632 can be maintained with a negative charge and the second conductor group 634 with a positive charge, resulting in a measurable capacitance in the electronic fabric probe 602.

[0075] The charge can be measured based on the capacitance between the first conductor group 632 and the second conductor group 634, and can be a function of the voltage and / or current applied to the first and second conductor groups and the distance between the first and second conductor groups. The distance or spacing between the first conductor group 632 and the second conductor group 634 corresponds to the diameter of the fluid chamber 604. Since the fluid chamber 604 is partially defined by a non-conductive fabric layer 620, which can have elastic or flexible characteristics as described above, the diameter of the fluid chamber 604 can be changed, for example, under the influence of the fluid pressure within the fluid chamber 604.

[0076] refer to Figure 11 An embodiment of the electrical sensor 600 is shown where the fluid pressure within the fluid chamber 604 is greater than the corresponding external pressure surrounding the electronic fabric probe 602. In this case, the fluid pressure causes the non-conductive fabric layer 620 to expand radially outward, thereby increasing the diameter of the fluid chamber 604, changing the proximity, and separating the electrode conductors of the first conductor group 632 from the electrode conductors of the second conductor group 634. The increased spacing between the electrode conductors 630 results in a change in capacitive charge and / or electric field in the electronic fabric probe 602 that can be measured by instruments in the associated circuitry. If the fluid pressure in the fluid chamber 604 decreases relative to the outside, the first and second conductor groups 632, 634 will move together, resulting in another measurable change in capacitance. In this embodiment, either the first conductor group 632 or the second conductor group 634 can be used as a reference by providing a second conductive element that electromagnetically interacts with the change in proximity between the groups.

[0077] By measuring changes in capacitance by altering the proximity of the electrode conductors, the electrical sensor 600 can measure changes in fluid pressure caused by various factors. For example, changes in fluid pressure may be caused by changes in fluid velocity, composition, etc. Furthermore, changes in fluid pressure can reflect displacements of other parts of the fluid circuit that can be detected by the electrical sensor. It is understood that other configurations for the electrical sensor to measure changes in fluid pressure by monitoring the dimensional proximity and capacitance between two or more sets of opposing conductors embedded in an electronic fabric probe are possible. For example, fluid pressure can be directed to the outside of the electrical sensor 600 to move the first and second sets of conductors toward each other, or the electrode conductors can be embedded in opposing fabric membranes disposed on either side of the fluid chamber and move together or apart in response to pressure changes. Additionally, one set of electrode conductors can be positioned in a fixed location, while another set of electrode conductors is attached to a flexible electronic fabric probe that allows relative displacement of the conductors.

[0078] In addition to using capacitance to measure changes in pressure or proximity, reference Figure 12An embodiment of an electrical sensor 700 with an electronic fabric probe 702 that utilizes inductance is shown. The electronic fabric probe 702 is supported by a rigid support 706 and exposed to a fluid chamber 704 defined within the rigid support 706. In this embodiment, the rigid support 706 may be configured as a square or rectangular hollow tube extending between a first end 710 and an opposite second end 710. Each of the first end 710 and the opposite second end 710 defines an opening 714 to receive and drain fluid through the fluid chamber 704. Thus, the electrical sensor 700 has an axial flow-through configuration; however, in other embodiments, the sensor may be blind-ended. The rigid support 706 may be made of a non-conductive material such as polycarbonate plastic.

[0079] To accommodate the electronic fabric probe 702 within the fluid chamber 704, the rigid support 706 may have an aperture 716 or a rectangular window extending through the body and located between the first and second ends 710, 712. The electronic fabric probe 702 may have a corresponding rectangular shape and may be attached to cover the aperture 716 by any suitable method, including adhesive bonding or acoustic welding. To support the electrode conductor and provide flexibility or suppleness, the electronic fabric probe 702 may comprise a non-conductive fabric layer 720 of any of the aforementioned materials, preferably an elastic material and fluid-impermeable. The non-conductive fabric layer 720 is a flexible planar sheet and may be cut to the shape of the aperture 716 to be placed on or surround the aperture.

[0080] To make the electronic fabric probe 720 sensitive to electromagnetic fields, the conductive element or electrode conductor 730 embedded in the non-conductive fabric layer 720 can be configured as a thin strip or wire wound into a coil. Specifically, the electrode conductor 730 may include multiple wound spirals that begin and terminate with a lead 734, which may be accessiblely exposed to the outside of the rigid support 706. Applying current to the lead 734 causes current to flow in the coil, generating a magnetic field around the electrode conductor 730 according to the principle of inductance. Furthermore, if the current changes or reverses direction, for example, by applying alternating current (AC) to the lead 734 of the electrode conductor 730, the resulting magnetic field will similarly change direction and / or amplitude. The magnetic field can penetrate through the non-conductive fabric layer 720. In various embodiments, the coil of the electrode conductor 730 may be wound around a conductive core, etc., to increase the strength of the generated magnetic field.

[0081] In response to interact with the generated magnetic field, a second conductive element 738, such as a conductive metal plate, can be disposed near the electrode conductor 730 as a reference. The second conductive element 738 can be parallel to and substantially co-extended with the electronic fabric probe 702, and can be fixed at a fixed position, for example, a few millimeters from the probe, to interact with the magnetic field. The magnetic field can induce an electromagnetic reaction in the second conductive element, which may result in reverse current or eddy current induction. Furthermore, if the generated magnetic field changes with the application of AC in the electrode conductor 730, the induced current or eddy current in the second conductive element 738 or the reference will also change. The changing eddy currents can cause a change in the inductance of the coil-shaped first electrode conductor 730, which can be measured by a suitable instrument or circuit connected to the lead 734.

[0082] Because the electronic fabric probe 702 is exposed to the flow chamber 704 through the hole 716, the non-conductive fabric layer 720 can deflect with changes in the fluid pressure within the flow chamber. Therefore, if the pressure increases, the non-conductive fabric layer 720 can shift toward the second conductive element 738, and if the pressure decreases, it can retract from the second conductive element. This displacement of the non-conductive fabric layer 720 thus alters the proximity of the electrode conductor 730 and the second conductive element 738 or reference relative to each other in a manner that has a measurable effect on the inductance of the first electrode conductor 730. By calibrating the internal pressure in the fluid chamber 704, the resulting displacement of the non-conductive fabric layer 720, and the change in inductance, the electrical sensor can indicate the pressure and / or flow rate of the fluid passing through the electrical sensor 700. In other embodiments, the arrangement of the electronic fabric probe 702, the flow chamber 704, and the rigid body defining the flow chamber can differ. Figure 12 The illustrations and descriptions provided include examples of different flow paths.

[0083] Sensor identification and verification

[0084] In a further embodiment, the electronic fabric probe can be configured to provide identification information and verification features to ensure that the electrical sensor is correctly installed in the medical device. (See also...) Figure 13For example, an embodiment of an electronic fabric probe 802 is shown, which can be mounted in a housing 804 for an electrical sensor 800 to sense fluid properties. The electronic fabric probe 802 includes a non-conductive fabric layer 810 in which a plurality of electrode conductors 812 are embedded. The non-conductive fabric layer 810 can be made of any of the aforementioned fluid-permeable or impermeable materials and can have flexible or resilient properties to facilitate mounting in the housing 804. The non-conductive fabric layer 810 can have any suitable shape depending on the application, including, for example, a tongue-shaped fabric sheet cut or stamped in the illustrated embodiment, including at least one side edge 814. In this embodiment, the plurality of electrode conductors 812 can be a series of elongated conductive strips or lines extending through the non-conductive fabric layer 810 and arranged generally parallel to each other. The plurality of electrode conductors 812 can be configured to sense the conductivity of a fluid guided through the fabric probe 802; however, in other embodiments, the electrode conductors 812 can be configured to sense other fluid properties, such as pressure or temperature. In this embodiment, the visual color of the plurality of electrode conductors 812 is preferably different from the color of the non-conductive fabric layer 810, so that these elements are visually distinguishable.

[0085] To enable the plurality of electrode conductors 812 to form electrical contact with corresponding leads or contacts disposed outside the electrical sensor 800, the electrode conductors may include terminal portions 816 terminating at and along the side edges 814 of the non-conductive fabric layer 802. Therefore, when the fabric probe 802 is housed within the housing 804 of the electrical sensor 800, the side edges 814 and terminal portions 816 of the electrode conductors 804 are accessible from outside the housing. In one embodiment, to identify and transmit information or data about the electronic fabric probe 802 and / or the electrical sensor 800, the terminal portions 816 of the plurality of electrode conductors 812 may be configured to form an identifiable pattern for transmitting identification information. In particular, because the terminal portions 816 are arranged in parallel and clearly spaced along the exposed side edges 814, they can provide a readable barcode based on their spacing, thickness, color, and / or contrast, etc. An optical scanner or machine reader can be used to scan the terminal portions 816 of the non-conductive fabric layer 810 and the exposed strip between the terminal portions 816 and interpret their settings in a manner that conveys information about the electronic fabric probe 802 and / or the electrical sensor 800. This information may be related to the brand and model of the sensor, its electrical or fluid characteristics or properties, its intended installation information, etc. In another embodiment, the identifiable pattern produced by the exposed terminals may represent other information, such as a visible indication on the left or right side for mating the electrical sensor with a mating connector.

[0086] refer to Figure 14This illustration shows another embodiment in which the electronic fabric probe 902 of the electrical sensor 900 is configured to provide identification and verification features. The electronic fabric probe 902 may include a non-conductive fabric layer 910 having planar flexibility and having a plurality of electrode conductors 912 embedded therein. Any of the foregoing materials and configurations described herein apply to the non-conductive fabric layer 910 and the plurality of electrode conductors 912. Similarly, the electrode conductors 912 may be elongated strips or lines arranged in parallel and including terminal portions 916 arranged perpendicularly along the side edges 914 of the non-conductive fabric layer 910 to enable electrical contact with a mating electrical connector of a corresponding circuit.

[0087] exist Figure 14 In this embodiment, the mating electrical connector 920 operatively associated with the electrical sensor 900 may include a planar plate 922, such as a printed circuit board, on which circuit traces are provided and configured to establish a board-to-board connection with the electronic fabric probe 902. The planar plate 922 may include a leading edge 924 oriented toward a side edge 914 of the fabric probe 902 and including a plurality of aligned conductive contacts 926. These conductive contacts 926 may be pins, forks, or springs that project vertically from or otherwise approach the leading edge 924 and are electrically connected to the traces on the planar plate 922. The plurality of conductive connector contacts 926 may be spaced apart and complementary, and sized to correspond to a plurality of terminal portions 916 along the side edge 914 of the electronic fabric probe 902 corresponding to the electrode conductor 912. When the electronic fabric probe 902 and the electrical connector 920 are moved together, the terminal portions 916 may slide into contact with the protruding connector contacts 926 to establish electrical communication between the components.

[0088] To verify the electrical sensor 900, in one embodiment, a mating electrical connector 920 may include at least a first connector contact 930 and a second connector contact 932 disposed on a leading edge 924 to contact a special-purpose or dedicated electrode conductor 918 on the electronic fabric probe 902. The first and second connector contacts 930, 932 may be spaced apart by a specific distance 934, corresponding in size and position to the distance between terminal portions 916 of the dedicated electrode conductor 918. The first and second connector contacts 930, 932 and the terminal portions 916 of the dedicated electrode conductor 918 are also aligned with each other with respect to the side edge 914 of the probe and the leading edge 924 of the plate 922 to ensure they achieve sliding contact with each other. The first and second connector contacts 930, 932 may be electrically coupled to a circuit or power supply via traces on the planar plate 922, and the dedicated electrode conductor 918 may be configured as a complete or closed circuit, thereby forming a verification or validation circuit. Therefore, the contact pattern between the first and second conductor contacts 930, 932 matches the dedicated electrode conductor 918 on the electronic fabric probe 902. The position and spacing between the first and second connector contacts 930, 932 and the terminal leads 916 of the dedicated electrode conductor 918 can be specified for different electrical sensors 900 to confirm the correct connection between the electrical sensor and the mating electrical connector 920. If the first and second conductor contacts 930, 932 and the dedicated electrode conductor 918 are misaligned, the confirmation circuit 938 will not close. The confirmation circuit 938 can be connected to a power switch, warning alarm, or other measures to prevent accidental use of the electrical sensor. In other embodiments, the dedicated electrode conductor 918 may include a plurality of electrode conductors 912, which may also be used as part of the sensing or excitation function of the electrical sensor.

[0089] Reference Figure 14 and Figure 15In a further embodiment, the electronic fabric probe 900 may include a second dedicated electrode conductor 950 or a set of electrode conductors embedded in a non-conductive fabric layer 910, which is configured as an antenna to transmit or transmit information about the electronic fabric probe 900. The antenna-shaped second dedicated electrode conductor 950 may be made of a conductive material strip or wire bent or shaped into a pattern for use as a radio frequency identification (“RFID”) tag. In one embodiment, the second dedicated electrode conductor 950 may be configured as a passive RFID, responding to an applied energy field emitted from an RF scanner 952 placed near and pointed at the electronic fabric probe 902. When an energy field of the correct frequency and / or wavelength is applied, a small response current may be generated in and conducted through the second dedicated electrode conductor 950. Furthermore, those currents may generate a responding electromagnetic field of radio waves in the form of a radio signal 954, which may be received by the RF scanner 952 or another scanner. For example, the transmitted radio signal 954 can be unique to the second dedicated electrode conductor 950 based on the conductor's shape, material properties, or other characteristics. The radio signal 954 can convey or represent information about the electronic fabric probe 900 in which the second dedicated electrode conductor 950 is embedded. An advantage of using RFID technology is that, because radio waves can penetrate many materials that may be used for the probe housing, the second dedicated electrode conductor 950 does not need to be located in an exposed position, for example, along the side edge 914. In embodiments where power is applied to the first electrode conductor 912 of the electronic fabric probe 902, the second dedicated electrode conductor 950 can be configured as an active device that receives power from the applied power to the first electrode conductor 912 to transmit radio signals, without requiring an activation or excitation field.

[0090] Shielded sensor

[0091] In another aspect, the electronic fabric probe used for an electrical sensor can be configured to provide electromagnetic shielding to an electrical conductor that can be embedded in a non-conductive fabric layer. (Reference) Figure 16 and Figure 17An embodiment for manufacturing an electrical sensor 1000 having a shielded electronic fabric probe 1002 is shown. The electronic fabric probe 1002 includes a non-conductive fabric layer 1010, which may be a planar rectangular strip of material as described above. Preferably, the material is relatively thin, has flexible or tough properties that allow it to be wrinkled or folded about itself, and is fluid-permeable. Any of the aforementioned non-conductive fabric materials can be used for the non-conductive fabric layer 1010. To define the rectangular shape, the non-conductive fabric layer 1010 may include a first side edge 1012 defining the width of the non-conductive fabric layer 1010 and a parallel second side edge 1014, as well as a first end edge 1014 and a second end edge 1016 defining the length of the non-conductive fabric layer 1010. As explained further below, embodiments of the non-conductive fabric layer 1010 may also be configured with first segments 1020, second segments 1022, and third segments 1024 about its longitudinal extension, such that these segments are generally quadrilateral. The first segment 1020, the second segment 1022, and the third segment 1024 may have approximately equal dimensions and may be separated by a first fold line 1026 and a second fold line 1028 (shown as dashed lines), the first fold line 1026 and the second fold line 1028 being perpendicular to the first and second side edges 1012, 1014 and parallel to the first and second end edges 1016, 1018.

[0092] In this embodiment, the electrode conductors 1030 embedded in the non-conductive fabric layer 1010 can be configured as a first conductor group 1032 and a second conductor group 1034. The first conductor group 1032 can be embedded in the middle second segment 1022 of the non-conductive fabric layer 1010, extending across its width between the first and second side edges 1012, 1014. The first conductor group 1032 can also be parallel to and limited by the first fold line 1026 and the second fold line 1028. The fold lines 1026, 1028 can be merely representative, or can be formed as creases, indentations, or perforations in the non-conductive fabric layer 1010. The electrode conductors 1030 of the first conductor group 1032 can again be fine parallel strips or lines of conductive material arranged separately from each other to maintain electrical isolation. In the illustrated embodiment, the electrode conductors 1030 of the first conductor group 1032 can be designated as active electrodes such as excitation electrodes or sensing electrodes, meaning that the conductors of the first conductor group 1032 are configured or intended for connection to a suitable instrument or power supply. In order to make electrical contact with a connector or circuit element, the electrode conductor 1030 of the first conductor group 1032 may protrude slightly beyond the first side edge 1014 and the second side edge 1016 of the non-conductive fabric layer 1010.

[0093] To provide shielding for the active electrodes in the first conductor group 1032, the second conductor group 134 may be embedded in the first and third segments 1020, 1024 of the non-conductive fabric layer 1010. Similar to the first conductor group 1032, the electrode conductors 1030 of the second conductor group 1034 may be parallel to each other and parallel to the fold lines 1026, 1028, such that they extend across the width of the non-conductive fabric layer 1010 perpendicular to the first and second side edges 1012, 1014; however, in other embodiments, the electrode conductors 1030 of the second conductor group 1034 may have different orientations or arrangements, such as diagonal arrangement, interconnect grids, etc. Furthermore, the individual electrode conductors 1030 of the second conductor group 1034 may have different dimensions or thicknesses relative to the electrode conductors 1030 in the first conductor group 1032. The electrode conductors 1030 of the second conductor group 1034 may be designated as passive electrodes, meaning they are not configured to be electrically connected to another circuit. As a passive electrode, the electrode conductor 1030 of the second conductor group 134 is electrically insulated from other circuits or electrical connectors that can be matched with the electrical sensor 1000.

[0094] To assemble the electrical sensor 1000, the first segment 1020 of the non-conductive fabric layer 1010 can be folded parallel to the first fold line 1026, as shown by arrow 1040, adjacent to and above the second segment 1022. The third segment 1024 can be folded about the second fold line 1028, as shown by arrow 1042, also adjacent to and below the middle segment 1024. The middle second segment 1022 is thus sandwiched between the opposing first segment 1020 and third segment 1024, and the first and second electrode groups are arranged in three separate and parallel planes. When mounted in a suitable electrical sensor, fluid can be guided through the adjacent first segment 1020, second segment 1022, and third segment 1024 to contact the electrode conductor 1030 therein. Since the passive second conductor group 1034 is included in the first and third sections 1020, 1024, they can isolate the active first conductor group 1032 located in the second section 1022 of the non-conductive fabric layer 1010 from electromagnetic interference.

[0095] For example, the applied external electromagnetic field is canceled out by the induced current in the passive second conductor group 1034 surrounding the active first conductor group 1034, so that the electromagnetic field does not interfere with the first conductor group due to the Faraday effect. To aid shielding, the electrode conductors 1030 of the second conductor group 1034 preferably extend across the entire width of the non-conductive fabric layer 1010 between the first and second side edges 1012, 1014. In different embodiments, the passive second conductor groups 1034 disposed in the first and third sections 1020, 1024 may be isolated or electrically interconnected to shield the active first conductor group 1032 disposed between the passive second conductor groups 1034. In addition to shielding the active first conductor group 1032, the passive second conductor groups 1034 may absorb electromagnetic waves emitted from the first conductor group to avoid interference with other electrical components. In one embodiment, the spacing between the individual elements of the second conductor group 1034 may be selected to make the electronic fabric probe sensitive to electromagnetic interference of a specific wavelength. In one embodiment, the second conductor group 1034 may be interconnected to provide a closed circuit, or it may be connected to an electrical ground to discharge any induced current. In a further embodiment, additional folds or different folding arrangements of active and passive electrodes may be utilized.

[0096] Diagnostic circuit

[0097] As described above, electronic sensors utilizing electronic fabric probes can be used for internal diagnostics using fluid circuits in medical devices. (See reference...) Figure 18 An embodiment of a circuit 1100 (shown in thin lines) using a first electrical sensor 1102 and a second electrical sensor 1103 of the type described herein to monitor fluid operations, such as the effectiveness 1104 of a filter disposed in a fluid circuit 1106 (shown in thick lines). The filter 1104 can be any suitable type of fluid filter and is disposed in the fluid circuit 1106 in such a manner that it divides the circuit into an upstream branch 1108 and a downstream branch 1110. Fluid flows from the upstream branch 1108 to the filter 1104, which removes contaminants and discharges purified fluid to the downstream branch 1110. A pump, such as a peristaltic tube pump, can be disposed in the fluid circuit 1106 to guide fluid through the fluid circuit 1106. In one embodiment, the fluid guided from the fluid circuit 1106 to the filter 1104 can be dialysate fluid comprising fresh or used dialysate. Besides using circuit 1100 to monitor fluid filtration, other embodiments of the circuit can also be used to monitor other fluid operations, such as measuring the introduction of chemicals or additives into the fluid, fluid ionization, etc.

[0098] To monitor the effectiveness of filter 1104 in removing contaminants from the fluid, a first electrical sensor 1102 is disposed in the upstream branch 1108 prior to filter 104 or other operations, and a second electrical sensor 1103 is disposed in the downstream branch 1110 after filter 104 or other operations. The first and second electrical sensors 1102, 1103 may include an electronic fabric probe 1120 having any of the aforementioned configurations. The electronic fabric probe 1120 may include a non-conductive fabric layer 1122 made of a flexible or tough non-conductive fabric material configured as a thin planar sheet. For use as electrodes, a plurality of electrode conductors, including at least a first electrode conductor 1124 and a second electrode conductor 1126, may be embedded in the non-conductive fabric layer 1122. The electrode conductors 1124, 1126 may be narrow conductive strips or lines woven, sewn, or adhered to the non-conductive fabric layer in a parallel manner. In one embodiment, to support the electronic fabric probe 1120 and establish fluid communication with the fluid in the loop 1106, the probe may be housed in a non-conductive probe housing 1128. The electronic fabric probe 1120 can be designed as a crossflow or throughflow type depending on the construction of the probe housing 1128.

[0099] In operation, if filter 1104 functions, the fluid in the upstream branch 1108 should be relatively more conductive than the fluid in the downstream branch 1110 because filter 1104 is required to remove charge carriers and conductive ions that may be equivalent to unwanted contaminants. Ions may include calcium (Ca). + chlorine Cl - Or any other unwanted ions. Therefore, if the filter is operating normally, the filtered fluid in the downstream branch 1110 will be relatively non-conductive. Circuit 1100 compares the electrical characteristics of the fluids measured by the first electrical sensor 1102 in the upstream branch 1108 and the second electrical sensor 1103 in the downstream branch 1110. In particular, circuit 1100 compares the voltage difference between the first and second electrical sensors 1102, 1103.

[0100] To compare voltage differences, circuit 1100 includes a comparator 1140 configured to be electrically connected to first and second electrical sensors 1102, 1103. Comparator 1140 may be an electronic device, such as a differential amplifier or similar integrated circuit device. Comparator 1140 may include a first input 1142 or a positive input connected to a common output 1146 and a second input 1144 or a negative input. The first input 1142 may be electrically connected to the first electrode conductor 1124 of the first and second electrical sensors 1102, 1103, and the second electrode conductor 1126 may be connected, for example, to another part of the circuit to communicate with a conductivity meter, etc. The common output 1146 of comparator 1140 may be connected to an indicator element such as a light-emitting diode (“LED”) 1150, an audio alarm, or a similar warning device. To facilitate operational control of comparator 1140, a feedback loop may connect output 1146 to the second input 1144. Comparator 1140 may follow the following electrical conventions based on signals applied to its first and second inputs 1142, 1144:

[0101] (Equation 3) If V + (1142)>V - (1144), then V out (1146) = 1;

[0102] (Equation 4) If V + (1142) <V - (1144), then V out (1146) = 0.

[0103] To apply voltage to circuit 1100, battery 1152 is connected via its positive terminal to second input 1144 and also to the first electrode conductor 1124 in second electrical sensor 1103. If the fluid in downstream electrical sensor 1103 is sufficiently non-conductive, the signal (i.e., voltage) applied to second input 1144 is relatively high relative to first input 1142, and according to Equation 4, output 1126 is zero. If filter 1104 becomes saturated or fails, the fluid in second electrical sensor 1103 becomes conductive relative to first electrical sensor 1102. Current from battery 1152 can flow from the first electrode conductor 1124 in downstream electrical sensor 103 to second electrode conductor 1126, causing the signal (i.e., voltage) on second input 1144 to decrease compared to first input 1142. Therefore, according to Equation 3, output 1146 goes high, causing LED 1150 to illuminate to indicate that filter 1104 needs replacement. Therefore, the aforementioned circuit 1100 uses a low-cost electronic fabric probe 1120 to monitor the usefulness of the filter 1104 or other operations located in the fluid circuit 1106 of the medical device.

[0104] All references cited in this article (including publications, patent applications and patents) are incorporated herein by reference to the same extent that each reference is individually and specifically indicated as incorporated by reference and fully elaborated herein.

[0105] Unless otherwise stated herein or obviously contradicted by the context, the terms “a,” “an,” and “the,” as well as “at least one” and similar designations, used in the context of describing the invention (particularly in the context of the claims below), shall be interpreted to cover both singular and plural cases. Unless otherwise stated herein or obviously contradicted by the context, the use of the term “at least one” (e.g., “at least one of A and B”) following a list of one or more items shall be interpreted to mean selection from the listed items (A or B) or any combination of two or more of the listed items (A and B). Unless otherwise stated, the terms “comprising,” “having,” “including,” and “containing” shall be interpreted as open-ended terms (i.e., meaning “including but not limited to”). Unless otherwise stated herein, the descriptions of numerical ranges herein are intended merely as a shortened way of referring individually to each individual numerical value falling within the range, and each individual numerical value is incorporated into the specification as if it were individually listed herein. Unless otherwise indicated herein or obviously contradicted by the context, all methods described herein may be performed in any suitable order. Unless otherwise stated, the use of any and all examples or exemplary language (e.g., "such as") provided herein is intended only to better illustrate the invention and does not limit the scope of the invention. No language in the specification should be construed as indicating that any unclaimed element is essential to the practice of the invention.

[0106] Preferred embodiments of the invention are described herein, including the best modes known to the inventors for carrying out the invention. Variations of those preferred embodiments will become apparent to those skilled in the art after reading the foregoing description. The inventors expect those skilled in the art to appropriately employ such variations, and the inventors intend that the invention be practiced in ways other than those specifically described herein. Therefore, the invention includes all modifications and equivalents of the subject matter recited in the appended claims as permitted by applicable law. Furthermore, unless otherwise stated herein or clearly contradicted by the context, the invention covers any combination of the foregoing elements in all possible variations.

Claims

1. An electrical sensor for use in a medical device, comprising: An electronic fabric probe having a non-conductive fabric layer and a plurality of conductors, including a first conductor and a second conductor, embedded in the fabric layer, the first conductor and the second conductor being spaced apart from each other and including corresponding first terminals and second terminals exposed near the peripheral edge of the fabric layer. A housing of a closed fluid chamber, the fluid chamber defining a flow path for fluid between a fluid inlet and a fluid outlet, the housing being adapted to house the electronic fabric probe, a first conductor and a second conductor being arranged in the flow path and configured to be electrically connected via the fluid to sense the electrical properties of the fluid, the first terminal and the second terminal being accessible from the outside of the housing; and An electrical connector configured to connect the plurality of conductors inside the fluid chamber to an electronic controller outside the fluid chamber; The electrical sensor has a crossflow configuration, with a fluid inlet arranged in the inlet region of the fluid chamber and a fluid outlet arranged in the exit region of the fluid chamber, and the fluid inlet and the fluid outlet pointing to the same surface of the fabric layer; The fluid chamber has an elongated oval shape, the inlet region is arranged at the first end, and the outlet region is arranged at the second end. as well as The electronic fabric probe is received in a recess arranged in the plane of the housing to maintain the planar configuration of the electronic fabric probe.

2. The electrical sensor according to claim 1, wherein, The fabric layer is a non-conductive mesh, and the first conductor and the second conductor are formed as conductive lines embedded in the non-conductive mesh.

3. The electrical sensor according to claim 2, wherein, The electrical sensor measures the electrical conductivity of the fluid.

4. The electrical sensor according to claim 3, wherein, The electrical sensor measures the voltage drop corresponding to the fluid, and the electronic controller is configured to use the voltage drop to determine the resistivity and / or conductivity of the fluid.

5. The electrical sensor according to claim 1, wherein, The fluid inlet and the fluid outlet are configured as hose fittings, and the electrical sensor is removable from the medical device.

6. The electrical sensor according to claim 5, wherein, The housing is made of molded plastic and includes a first housing portion and a second housing portion, which can be disassembled to access the fluid chamber and remove and replace the electronic fabric probe.

7. A dialysis machine, comprising: A dialyzer, which defines the dialysate side and the blood side separated by a membrane; A fluid source, which supplies fluid in the liquid phase; At least one fluid line delivers the fluid to the dialyzer; A pump, which is disposed in the at least one fluid line, is used to direct fluid to or out of the dialyzer; An electrical sensor, disposed in the at least one fluid line, includes an electronic fabric probe housed in a housing that closes a fluid chamber having a fluid inlet and a fluid outlet connected to the at least one fluid line. The electronic fabric probe has a non-conductive fabric layer in which a first conductor and a second conductor are embedded. The first conductor and the second conductor are arranged in a flow path defined by the housing and spaced apart from each other. The electrical sensor also includes an electrical connector configured to connect the first conductor and the second conductor to an electronic controller outside the fluid line. as well as The electronic controller is electrically connected to the electrical sensor and in electronic communication with the first conductor and the second conductor. The electronic controller is operatively associated with a human-machine interface for displaying information about the fluid, the information being determined by the electrical communication between the first conductor and the second conductor via the fluid. The electronic controller is configured to determine the resistivity and / or conductivity of the fluid based on the parameters of the fluid measured by the first conductor and the second conductor. The electrical sensor has a crossflow configuration, the fluid inlet is arranged in the inlet region of the fluid chamber, the fluid outlet is arranged in the exit region of the fluid chamber, and the fluid inlet and the fluid outlet point to the same surface of the fabric layer; The fluid chamber has an elongated oval shape, the inlet region is arranged at the first end, and the outlet region is arranged at the second end. The electronic fabric probe is received in a recess arranged in the plane of the housing to maintain the planar configuration of the electronic fabric probe.

8. The dialysis machine according to claim 7, wherein, The fabric layer is a non-conductive mesh, and the first conductor and the second conductor are formed as conductive lines embedded in the non-conductive mesh.

9. The dialysis machine according to claim 7, wherein, The electrical sensor measures the voltage drop corresponding to the fluid.

10. The dialysis machine of claim 7, wherein the electrical sensor is removable from the fluid line.

11. The dialysis machine according to claim 10, wherein, The housing is made of molded plastic and includes a first housing portion and a second housing portion, which can be disassembled to access the fluid chamber and remove and replace the electronic fabric probe.

12. A method for monitoring fluid flowing in a fluid line of an electrical instrument for non-therapeutic purposes, the method comprising: The electrical sensor is connected via an electrical connector to an electronic controller operatively associated with the electrical instrument, the electrical sensor including an electronic fabric probe housed in a fluid chamber defined by the housing of the electrical sensor; The fluid is guided into the fluid chamber through the fluid inlet of the housing; Current or voltage is applied to the fluid in the fluid chamber via a first conductor embedded in the fabric layer of the electronic fabric probe, and a second conductor is arranged in the fabric layer of the electronic fabric probe and spaced apart from the first conductor; Measure the voltage drop across the first and second conductors of the electronic fabric probe; Based on the measured voltage drop, the resistivity and / or conductivity of the fluid in the fluid chamber are sensed via the second conductor; as well as Discard the electronic fabric probe after use; The electrical sensor has a crossflow configuration, the fluid inlet is arranged in the inlet region of the fluid chamber, the fluid outlet is arranged in the exit region of the fluid chamber, and the fluid inlet and the fluid outlet point to the same surface of the fabric layer; The fluid chamber has an elongated oval shape, the inlet region is arranged at the first end, and the outlet region is arranged at the second end. as well as The electronic fabric probe is received in a recess arranged in the plane of the housing to maintain the planar configuration of the electronic fabric probe.

13. The method of claim 12, further comprising: Replace the discarded electronic fabric probe with another electronic fabric probe and reassemble the housing of the electrical sensor.

14. The method according to claim 12, wherein, The fabric layer is a non-conductive mesh, and the first conductor and the second conductor are formed as conductive lines embedded in the non-conductive mesh.

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