US20040254513A1 - Conductive polymer materials and applications thereof including monitoring and providing effective therapy - Google Patents

Abstract

Conductive materials and devices, apparatuses, systems and methods that employ same. The conductive material can include a conductive polymer material that can be utilized to monitor one or a combination of conditions during patient therapy, such as patient access, solution compounding and the like. This can facilitate the safe and effective administration of patient therapy, such as dialysis therapy.

Description

CROSS REFERENCE TO RELATED APPLICATIONS
• This patent application is a continuation-in-part of U.S. patent application Ser. No. 10/121,006 filed on Apr. 10, 2002.[0001]
BACKGROUND OF THE INVENTION
• The present invention relates generally to conductive polymer materials and methods of preparing and employing same. More specifically, the present invention relates to conductive polymer materials and applications thereof including monitoring patient access disconnection, monitoring solution mixing and compounding and the like during medical therapy, such as dialysis therapy.[0002]
• A variety of different medical treatments relate to the delivery of fluid to and/or from a patient, such as the delivery of blood between a patient and an extracorporeal system connected to the patient via a needle or needles or any suitable access device inserted within the patient. For example, hemodialysis, hemofiltration and hemodiafiltration are all treatments that remove waste, toxins and excess water directly from the patient's blood. During these treatments, the patient is connected to an extracoporeal machine, and the patient's blood is pumped through the machine. Waste, toxins and excess water are removed from the patient's blood, and the blood is infused back into the patient. Needles or other suitable access devices are inserted into the patient's vascular access in order to transfer the patient's blood to and from the extracoporeal machine. Traditional hemodialysis, hemofiltration and hemodiafiltration treatments can last several hours and are generally performed in a treatment center about three to four times per week.[0003]
• During any of these hemo treatments, dislodgment of the access device can occur, such as dislodgment of a needle inserted into the patient's vascular access including an arterio-venous graft or fistula. If not detected immediately, this can produce a significant amount of blood loss to the patient. The risks associated with a needle dislodgment are considerable. In this regard, important criteria for monitoring blood loss include, for example, the sensitivity, specificity and response time with respect to the detection of needle dislodgment. With increased levels of sensitivity, specificity, and response time, the detection of needle dislodgment can be enhanced, and blood loss due to dislodgment can be minimized.[0004]
• Typically, patients undergoing medical treatment, such as hemodialysis, hemofiltration or hemodiafiltration, are visually monitored in order to detect needle dislodgment. However, the needle may not be in plain view of the patient or medical staff (i.e., it may be covered by a blanket) such that it could delay detection and, thus, responsive actions to be taken in view of dislodgment, such as stopping the blood pump of the extracorporeal machine to minimize blood loss to the patient.[0005]
• Moreover, in view of the increased quality of life, observed reductions in both morbidity and mortality and lower costs than in-center treatments, a renewed interest has arisen for self care and home hemo therapies. Such home hemo therapies (whether hemodialysis, hemofiltration or hemodiafiltration) allow for both nocturnal as well as daily treatments. During these self care and home hemo sessions, especially during a nocturnal home hemo session, when the patient is asleep, dislodgment risks are more significant because nurses or other attendants are not present to detect the dislodgment.[0006]
• Although devices that employ a variety of different sensors are available and known for detecting and/or monitoring a variety of different bodily fluids, these devices may not be suitably adapted to detect needle dislodgment. For example, known devices that employ sensors including pH, temperature and conductivity have been utilized to detect bedwetting and diaper wetness. Further, devices that employ pressure sensors and/or flow sensing devices are known and used during medical treatment, such as dialysis therapy, to monitor fluid flow including blood flow to and/or from the patient. However, these types of detection devices may not provide an adequate level of sensitivity and responsiveness if applied to detecting blood loss from the patient due to needle dislodgment. Although venous pressure is known to be used to monitor needle dislodgment, it is not very sensitive to needle drop-out.[0007]
• Additional other devices and methods are generally known to monitor vascular access based on the electrical conductivity of blood. For example, Australian Patent No. 730,338 based on PCT Publication No. WO 99/12588 employs an electrical circuit which includes two points through which current is induced in blood flowing through an extracorporeal circuit in a closed loop. Electrical current is induced by means of a coil that is placed around the outside of the tubing of the blood circuit. Thus, each coil does not directly contact the blood as it circulates through the tubing. In this regard, an electrical current is induced in the blood loop by an alternating current that flows through one of the coils. The second coil is then utilized to measure a change in amperage of the induced current as it flows through the blood circuit.[0008]
• In this regard, electrical current is coupled to a blood treatment system that includes a number of high impedance components, such a blood pump, air bubble traps, pinch clamps and/or the like. Because of the large impedance of the conducting fluid loop (due to the peristaltic pump and other components), the induction and detection of a patient-safe current requires an impractically complex design of the coil and system. Further, a high level of noise would necessarily result from the use of such levels of induced current. This can adversely impact the sensitivity of detection. If lower currents are used, the field coil would have to be increased in size to detect such low current levels. This may not be practical in use, particularly as applied during dialysis therapy.[0009]
• PCT Publication No. WO 01/47581 discloses a method and device for monitoring access to the cardiovascular system of a patient. The access monitoring employs an electrical circuit which can generate and detect a current at separate points along a blood circuit connected to the patient. Electrical current is coupled to the blood using capacitive couplers that each have a metal tube placed around the blood circuit tubing. In this regard, the metal tube defines a first plate of a capacitor; the blood circuit tubing defines the dielectric; and the blood inside of the blood circuit tubing defines the second plate of the capacitor.[0010]
• The generator applies a potential difference between a pair of points to generate a current in a segment of the blood circuit. A detector utilizes an additional and separate pair of contact points to measure the current along at least one section of the venous branch between a first contact point and the venous needle. The change in voltage (dV) can then be determined based on a measured change in current and compared to a reference range (I) to monitor access conditions. In this regard, PCT Publication No. WO 01/47581 requires a complex circuit design that utilizes multiple sets of capacitive couplers to monitor vascular access conditions. This can increase the cost and expense of using same.[0011]
• Further, the mere use of capacitive coupling to inject an electric signal in the blood circuit and/or for detection purposes can be problematic. In this regard, the signal must pass through the tubing of the blood circuit as the tubing acts as a dielectric of the capacitor. This may cause an excess level of noise and/or other interference with respect to the detection of changes in vascular access conditions.[0012]
• In this regard, it is believed that known devices, apparatuses, systems, and/or methods that can be used to monitor a patient's access conditions may not be capable of detecting change in access conditions, such as in response to needle drop-out, with sufficient sensitivity and specificity to ensure immediate detection of blood loss such that responsive measures can be taken to minimize blood loss. As applied, if twenty seconds or more of time elapses before blood loss due to, for example, dislodgment of the venous needle, over 100 milliliters in blood loss can occur at a blood flow rate of 400 ml/min, which is typical of dialysis therapy. Thus, the capability to respond quickly upon immediate detection of dislodgment of an access device, such as a needle, from a patient is essential to ensure patient safety.[0013]
• In addition to dislodgement, additional other parameters are, in general, monitored to evaluate changes thereof during medical procedures including dialysis therapy. For example, temperature sensors, pressure sensors, conductivity sensors and the like are generally known and used in a variety of ways to detect and monitor condition changes during medical therapy.[0014]
• As applied to dialysis therapy and the like, a dialysis solution can be administered to a patient in mixed form. In this regard, the extent to which the solution is mixed can have an impact on the effectiveness of the associated therapy. In dialysis therapy, the solutions may have varying pH levels that are at levels considered to be non-physiologic prior to mixing, while after mixing, the final solution is required to have a pH at a physiological level necessary for effective and safe administration during therapy. In general, conductivity sensors and pH sensors are known and used. However, it is believed that known sensors may not be as effective in terms of detection capabilities and relative ease of use, particularly as applied during dialysis therapy.[0015]
• Accordingly, efforts have been directed at designing apparatuses, devices, systems and methods for improved monitoring of patient therapy, such as detecting changes in patient access conditions in response to needle dislodgment, detecting changes in solution compounding and mixing, and the like, wherein detection is sensitive, specific and immediate in response to such changes such that responsive measures can be suitably taken to provide the patient with effective therapy, such as dialysis.[0016]
SUMMARY OF THE INVENTION
• The present invention provides improved devices, apparatuses, systems and methods that utilize electrically conductive materials to monitor a variety of different conditions or parameter changes associated with the administration of one or more solutions during medical therapy. In turn, this can facilitate the safe and effective administration of the medical therapy, such as dialysis therapy.[0017]
• In an embodiment, the conductive material includes a polymer conductive material that can include, for example, a polymer conductive component or a polymer matrix and a separate conductive component that is incorporated within the polymer matrix. The conductive materials of the present invention can be utilized in a number of different applications. For example, the conductive materials, such as the conductive polymer material, can be employed to monitor solution mixing and compounding. This can be utilized to evaluate whether the solution or solutions have been effectively mixed prior to administration during therapy. This can be determined by monitoring a pH change in the solution based on changes in conductivity. In this regard, the solution can be derived from a mixture of solution components with varying pH levels, such as between about 1.8 to about 9.2. Thus, the present invention can be utilized to determine whether the pH of the mixed solution is effectively maintained prior to use.[0018]
• The present invention provides improved devices, apparatuses, systems, and methods for detecting dislodgment or disconnection of an access device, such as dislodgment of a needle inserted in a patient during dialysis therapy. The devices, apparatuses, systems, and methods of the present invention utilize an electrical circuit with a number of electrical contacts which are in fluid contact with the fluid circuit such that an electrical signal can be injected into at least a segment including, for example, a loop defined along at least a portion of the conducting fluid circuit. In this regard, a direct-contact measurement can be used to provide immediate detection of a change in an electrical value in response to a change in access conditions, such as a change in impedance due to dislodgment of a needle or other access device from the patient during medical therapy including, for example, dialysis therapy and medication delivery.[0019]
• An advantage of the present invention is to provide an improved device, apparatus, system and/or method for monitoring patient therapy, such as for detecting patient access disconnection, for monitoring solution compounding and the like.[0020]
• Another advantage is to provide devices, apparatuses, systems and methods that employ electrically conductive materials, such as conductive polymer materials, to monitor patient therapy, such as dialysis.[0021]
• A further advantage of the present invention is to provide an improved device, apparatus, system and/or method for detecting dislodgment of an access device from a patient during medical therapy including dialysis therapy.[0022]
• Yet another advantage of the present invention is to provide a sensitive, specific and responsive apparatus and/or device for monitoring patient therapy, such as for detecting access disconnection during selfcare and home hemo treatments and for monitoring solution mixing conditions, such as pH changes, prior to use.[0023]
• Moreover, an advantage of the present invention is to provide a viable device or apparatus for allowing a patient or other non-medical personnel in a non-medical facility to administer a dialysis therapy that uses a portion of the patient's circulatory system.[0024]
• Furthermore, an advantage of the present invention is to provide an improved device, system and method for monitoring and/or controlling blood loss from a patient.[0025]
• Yet another advantage of the present invention is an improved device for connecting an electrical contact to a fluid circuit allowing fluid and electrical communication between the electrical contact and fluid flowing through the fluid circuit.[0026]
• Yet a further advantage of the present invention is to facilitate the safe and effective administration of medical therapy, such as dialysis therapy.[0027]
• Additional features and advantages of the present invention are described in, and will be apparent from, the following Detailed Description of the Invention and the figures.[0028]
BRIEF DESCRIPTION OF THE FIGURES
• FIG. 1A illustrates a schematic view of an embodiment of the present invention showing two needles insertable within a patient through which blood flows to and from an extracorporeal system.[0029]
• FIG. 1B illustrates a schematic view of an embodiment of the present invention capable of detecting needle dislodgment during dialysis therapy.[0030]
• FIG. 1C illustrates a perspective view of an embodiment of the present invention showing access disconnection detection capabilities during medical therapies administered via a single needle.[0031]
• FIG. 2A illustrates an exploded view of an electrical contact coupling device in an embodiment of the present invention.[0032]
• FIG. 2B illustrates a side sectional view of the coupling device of FIG. 2A in an embodiment of the present invention.[0033]
• FIG. 2C illustrates another embodiment of the coupling device of the present invention.[0034]
• FIG. 2D illustrates another embodiment of the coupling device of the present invention showing a threaded engagement between the components of same.[0035]
• FIG. 2E illustrates a sectional view of FIG. 2D.[0036]
• FIG. 3 schematically illustrates an embodiment of the present invention relating to processing of a measurable voltage signal to correct for changes in baseline impedance during treatment.[0037]
• FIG. 4A schematically illustrates a hemodialysis machine in an embodiment of the present invention.[0038]
• FIG. 4B schematically illustrates a hemodialysis machine coupled to a patient's access via a tubing set in an embodiment of the present invention.[0039]
• FIGS. 5A and 5B illustrate a coupler according to an embodiment of the present invention.[0040]
• FIG. 6 illustrates a dialyzer according to an embodiment of the present invention.[0041]
• FIGS. 7A and 7B illustrate a sensor assembly according to an embodiment of the present invention.[0042]
• FIGS. 8A and 8B illustrate a single-piece sensor according to an embodiment of the present invention.[0043]
• FIG. 9 illustrates a multi-chamber bag according to an embodiment of the present invention.[0044]
• FIG. 10 illustrates a multi-chamber bag with a peelable seal according to an embodiment of the present invention.[0045]
• FIG. 11 illustrates an automated peritoneal dialysis system according to an embodiment of the present invention.[0046]
DETAILED DESCRIPTION OF THE INVENTION
• The present invention generally relates to electrically conductive materials that can be effectively employed to monitor patient therapy. This can facilitate the safe and effective administration of patient therapy, such as dialysis therapy. In an embodiment, the conductive materials of the present invention include a conductive polymer material as described below in greater detail.[0047]
• The present invention provides medical devices, apparatuses, systems and methods for detecting access disconnection. More specifically, the present invention provides medical devices, apparatuses, systems, and methods that employ, in part, an electrical circuit with electrical contacts in fluid contact and electrical communication with a fluid circuit allowing a direct conductivity measurement to be used such that dislodgment of a needle or other access device through which fluid flows between a patient and the fluid circuit can be immediately detected. In this regard, fluid loss (i.e., blood loss) due to, for example, dislodgment of a needle from a patient undergoing medical treatment, such as dialysis therapy, medication delivery or the like, can be controllably minimized. In an embodiment, the conductive polymer materials of the present invention can be utilized to monitor solution compounding and mixing to ensure effective administration of the mixed solution during therapy, such as to determine whether a pH level of the mixed solution is effectively maintained prior to use.[0048]
• It should be appreciated that the present invention is not limited to the detection of needle dislodgment but can be utilized to detect the dislodgment or disconnection of any suitable access device. As used herein, the term “access disconnection” or other like terms means any suitable condition or event which can cause a loss or leak of an electrically conductive fluid flowing along a fluid circuit connected to the patient provided that a change in the electrical continuity between electrical contacts coupled to the fluid circuit can be detected. It should be appreciated that a change in the electrical continuity as measured by an electrical value, such as impedance, may be detected even in the absence of dislodgment of an access device from the patient. The term “access device” as used herein or other like terms means a suitable device that can be inserted within a patient such that fluid, including blood, can pass to, through and/or from the patient via the access device. The access device can include a variety of different and suitable shapes, sizes and material make-up. Examples of an access device includes needles, catheters, cannulas or the like. The access device can be composed of any suitable material including, for example, stainless steel, plastic or like biocompatible materials.[0049]
• Although in the embodiment set forth below the apparatus and/or device is designed for use in a dialysis therapy, such as hemodialysis, hemofiltration or hemodiafiltration, it should be noted that the present invention can be used in a number of different medical therapies that employ a variety of different and suitable fluid systems, such as extracorporeal blood systems. For example, the invention of the present application can be used during intravenous infusion that can employ the use of a single needle insertable within the patient for delivering a medical solution or drug, blood, blood products, processed blood or the like between the patient and the fluid system. In addition, the present invention can be used in plasma exchange therapies, where a membrane is used to separate whole blood into plasma and cellular components.[0050]
• With respect to dialysis therapy, the present invention can be used in a variety of different therapies to treat kidney failure. Dialysis therapy as the term or like terms are used throughout the text is meant to include and encompass any and all forms of therapies that utilize the patient's blood to remove waste, toxins and excess water from the patient. Such therapies include both intermittent, including hemodialysis, hemofiltration and hemodiafiltration, and continuous therapies used for continuous renal replacement therapy (CRRT). These continuous therapies include slow continuous ultrafiltration (SCUF), continuous veno-venous hemofiltration (CVVH), continuous veno-hemodialysis (CVVHD), and continuous veno-venous hemodiafiltration (CVVHDF). Dialysis therapy can also include peritoneal dialysis, such a continuous ambulatory peritoneal dialysis, automated peritoneal dialysis and continuous flow peritoneal dialysis. Further, although the present invention, in an embodiment, can be utilized in methods providing a dialysis therapy for patients having chronic kidney failure or disease, it should be appreciated that the present invention can be used for acute dialysis needs, for example, in an emergency room setting. Lastly, as one of skill in the art appreciates, the intermittent forms of therapy (i.e., hemofiltration, hemodialysis and hemodiafiltration) may be used in the in center, self/limited care as well as the home settings.[0051]
• In an embodiment, the present invention includes an electrical circuit with a number of electrical contacts, preferably a pair of electrical contacts, in fluid contact and electrical communication with the fluid circuit. The electrical contacts can include any suitable device through which electrical connection can be made with the fluid circuit thereby defining a conductive pathway or conductor loop therein. In an embodiment, at least one of the electrical contacts includes a conductive polymer material as described below in greater detail. Changes in an electrical value or any suitable parameter associated with the conductor loop can then be monitored in response to changes in access conditions as described below. In an embodiment, the electrical contact includes an electrode which can be coupled to the fluid circuit such that an electrical connection can be made in fluid contact with fluid flowing through the fluid circuit as discussed below.[0052]
• For example, a constant current or other suitable electrical signal can be injected into the fluid circuit via an electrode pair in contact with the fluid flowing in between the electrodes thereby defining a loop along at least a portion of the conducting fluid circuit. A change in an electrical value, preferably impedance, can then be measured in response to access disconnection. This can provide a direct conductivity measurement capable of detecting a change in impedance or other suitable electrical parameter of the fluid, such as an electrically conductive fluid including blood, medical solutions or the like, as it flows between a patient and a fluid system (i.e., an extracorporeal blood system) via a needle, needles or other access device(s) inserted within the patient.[0053]
• In this regard, the present invention can effectively detect dislodgment of a needle (e.g., a venous needle and/or an arterial needle) or other access device through which blood or other suitable fluid can flow, for example, to, through, and from the patient, such as a blood circuit used during dialysis therapy. The detection capability of the present invention is believed to be immediate based on the measurable change in, for example, impedance of the electrically conductive fluid or fluids due to fluid loss resulting from disconnection of the access device from the patient.[0054]
• The immediate detection capabilities of the present invention are important, particularly as applied to dialysis therapy where a significant amount of blood loss can occur within a relatively short period of time if delays in detection and responsive actions to stop the blood loss occur. Under typical dialysis conditions, if 20 seconds or more time elapses before blood loss due to dislodgrnent is detected and stopped, over 100 milliliters of blood can be lost based on typical blood flow rates of 400 milliliters/minute.[0055]
• Applicants have discovered that the present invention can detect access disconnection, particularly in response to venous needle dislodgment during dialysis therapy, with a high degree of sensitivity and specificity in addition to its immediate detection capabilities. The direct-contact measurement of the present invention is capable of detecting a change of an electrical value, preferably impedance, due to needle dislodgment or the like as the blood flows through the blood circuit during dialysis therapy. As used herein, the term “electrical value” or other like terms means any suitable electrical parameter such as, impedance, resistance, voltage, current, rates of change thereof and combinations thereof. The detection of a change in impedance or the like is an indication that the needle has become dislodged or other like condition has occurred. It is noted that the detection capabilities of the present invention can also effectively detect blood loss during medical therapy resulting from a disconnection in the fluid circuit, even if the needle or needles have not become dislodged. In this regard, the present invention can be effectively utilized to controllably minimize blood loss from the patient based on the ability of the present invention to immediately measure a change in impedance or the like due to blood loss with a high degree of sensitivity and specificity. This can facilitate the safe and effective administration of patient therapy as previously discussed.[0056]
• The devices and apparatuses of the present invention can include a variety of different components and configurations depending on the applied medical therapy such that fluid loss, particularly blood loss due to needle dislodgment or the like, can be effectively monitored.[0057]
Multiple Access Disconnection
• Referring now to FIG. 1A, an embodiment of the[0058]apparatus10 of the present invention includes a pair ofelectrical contacts12 in fluid contact with a blood tubing set14 of ablood circuit16. Theblood circuit16 connects a patient18 to anextracorporeal blood system20 as applied to, for example, dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration, continuous renal replacement or the like or plasma therapies. The pair ofelectrical contacts12 includes a firstelectrical contact22 and a secondelectrical contact24 which are attached to a respectivefirst tube member26 andsecond tube member28 of theblood circuit16. Thefirst tube member26 is connected to a venous needle or other suitable access device inserted into a vascular access region (not shown) of the patient. Thesecond tube member28 is connected to an arterial needle or the like also inserted into a vascular access region (not shown) of the patient. During dialysis therapy, for example, blood flows from the patient18 through the arterial needle to theextracorporeal blood system20 that includes, for example, a dialysis machine, via thesecond tube member28 where the blood is treated and delivered to the patient18 through the venous needle via thefirst tube member26.
• As the blood flows through the blood circuit during dialysis therapy, a constant electric current or the like generated by a[0059]controller29 can be injected or passed into the flowing blood via the electrical contact pair, preferably an electrode pair as described below. In an embodiment, at least one additional electrode can also be utilized in any suitable manner.
• The electrode pair connected to the[0060]controller29 or other suitable electronic device can then be used to measure a voltage change across an unknown fluid (e.g., blood) impedance or other like electrical value to detect a change in impedance or the like across the vascular access region. In an embodiment, one electrode can be used to inject the electrical signal into the fluid circuit while the other electrode of the pair can be used to sense a change in the electrical value and pass an electrical signal indicative of the same to the controller for processing and detection purposes. Upon dislodgment of at least one of the venous needle and arterial needle from the blood circuit or other suitable condition, an immediate and detectable increase in impedance or the like can be measured as compared to the impedance or other suitable parameter measured under normal operating conditions.
• It should be appreciated that the present invention as embodied in FIG. 1A can be modified in a variety of suitable ways depending on the medical therapy as applied. For example, the venous and arterial needles can be inserted into the vascular access of the patient on any suitable part of the patient's body, such as the upper arm, lower arm, upper thigh area or the like during dialysis therapy. As previously discussed, the present invention can be applied to a variety of different medical therapies including intravenous infusions, plasma exchanges, medication delivery, drug delivery, blood delivery and dialysis therapies (i.e., hemofiltration, hemodialysis, hemodiafiltration and continuous renal replacement).[0061]
• As illustrated in FIG. 1B, an embodiment of an[0062]apparatus30 of the present invention is shown as applied during dialysis therapy. In an embodiment, the present invention includes avenous needle32 andarterial needle34 inserted within apatient access36. Thevenous needle32 andarterial needle34 are connected to thedialysis system35 via a number oftube members38 that connect the various components of thedialysis system35 including, for example, avenous drip chamber40, adialyzer42, anarterial drip chamber44 and ablood pump46. It should be appreciated that one or more of the components of the dialysis system can be provided within a dialysis machine coupled to the blood circuit. As shown in FIG. 1B, a first electricalcontact coupling device48 and a second electricalcontact coupling device50 are positioned between thedialysis system35 and thevenous needle32 and thearterial needle34. As used herein, the term “electrical contact coupling device,” “coupling device” or other like terms means any suitable device that can be used to connect an electrical contact to the fluid circuit. In an embodiment, the electrical contact coupling device can be used to contact the electric contact to the fluid circuit allowing fluid contact and electrical connection with the fluid flowing through the fluid circuit as described below.
• In an embodiment, the electrical contact pair, preferably an electrode pair, is connected to a[0063]controller52 or other suitable electronic device. The controller can be used to inject an electric signal via the electrode pair and into the blood and/or other fluid as it flows through the blood circuit. This provides a conductor loop along which changes in electrical parameters or values can be measured. Thecontroller52 which is coupled to the electrode pair can also be used to measure this change. It should be appreciated that the controller can include a single electronic device or any suitable number of devices in electrical connection with the electrical contacts to input an electrical signal into the blood circuit thereby defining a conductor loop, to measure a change in an electrical parameter or value associated with the conductor loop and/or perform any other suitable tasks, such as processing the detectable signal as discussed below.
• Preferably, the electrical signal is generated from a constant current that is supplied to the electrodes until dislodgment occurs. The voltage across an unknown impedance of the fluid (e.g., blood) circulating through the blood circuit can then be measured (not shown) to detect a change in impedance due to changes in access conditions. However, it should be appreciated that any suitable electrical parameter and changes thereof can be monitored to detect needle drop-out or the like as previously discussed.[0064]
• As demonstrated below, the detection capabilities of the present invention are highly sensitive, specific and virtually immediate in response to access disconnection, such as needle dislodgment. Further, the electronic circuit of the present invention is relatively simple in design such that preferably one electrode pair is necessary to conduct direct conductivity measurement. This can reduce costs and effort as compared to known vascular access monitoring techniques that only employ non-invasive detection techniques, such as, capacitive couplers and induction coils as previously discussed.[0065]
• Applicants have discovered that the total impedance measured (“Z”) can be modeled as two lumped impedances in parallel with one impedance (“Z[0066]_D”) being produced by the pump segment, the dialyzer, the drip chambers and/or other suitable components of the dialysis system and/or the like. The other impedance component (“Z_P”) is formed by the patient's vascular access and associated tubing which carries blood to and from the vascular access and/or the like. In this regard, the total impedance measured can be characterized as a function of both Z_Dand Z_Pas follows:
• Z=(1/Z_D+1/Z_P)⁻¹
• Despite this parallel impedance, Applicants have discovered that the electrical contacts in connection with the controller can be used to measure a change in impedance along the conductor loop as blood flows through the blood circuit in response to access disconnection, such as needle dislodgment. If needle dislodgment occurs, the conductor loop along at least a portion of the fluid circuit changes from a closed circuit to an open circuit and thus Z=Z[0067]_Dwhere Z_Papproaches infinity. In this regard, the direct conductive measurement capabilities of the present invention can be effectively used to detect access disconnection.
• Applicants note that the Z[0068]_Dcomponent can produce a level of electrical interference associated with the time-varying high impedance of the components of a medical system coupled to the fluid circuit, such as a dialysis system and its components including, for example, a blood pump, a drip chamber and/or the like. Applicants have discovered that the interference due to the Z_Dcomponent can be effectively eliminated, or at least reduced, if necessary. In an embodiment, the signal associated with the detection of Z or the like can be further processed as discussed below. Alternatively, in an embodiment, the electrical circuit of the present invention can be designed to block or bypass one or more components of the dialysis system from the conductor loop or pathway defined along the blood circuit as described below. In this regard, the accuracy, sensitivity and responsiveness with respect to the detection of access disconnection can be enhanced.
• In an embodiment, a third[0069]electrical contact point53 can be utilized to minimize or effectively eliminate the interferences with respect to the high impedance components coupled to the blood circuit, such as the blood pump and the like. The additional contact point can be made in any suitable way. For example, the third contact point can be an electrode or other suitable device through which electrical continuity can be established between it and one of the electrodes of the coupling devices. In an embodiment, the third electrical contact can be attached to a fluid circuit in fluid and electrical communication with fluid flowing through same.
• The[0070]third contact point53 can be positioned at any suitable position along the blood circuit. Preferably, thethird contact point53 is positioned at any suitable location between theblood pump46 and thecoupling device50 as shown in FIG. 1B. An equalization potential can then be applied between thethird contact point53 and the electrode of thecoupling device50. The potential is applied at a voltage that is equal to the potential applied between the electrodes of thefirst coupling device48 and thesecond coupling device50.
• This effectively causes the electric current or the like, once injected into the blood circuit, to bypass one or more of the components of the dialysis system. In an embodiment, the[0071]third contact point53 can be positioned such that the electric current or the like would effectively bypass all of the components of the dialysis system as shown in FIG. 1B.
Single Access Disconnection
• The electrical contacts of the present invention can be positioned in any suitable location relative to the needle, needles or suitable access device inserted within the patient. As illustrated in FIG. 1C, an embodiment of the present invention as applied with respect to the detection of access detection, such as the dislodgment of a single access device inserted within the patient is shown. This type of application is applicable to a variety of different and suitable medical therapies administered via a single access device, such as a single needle, including intravenous infusion and dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement.[0072]
• As applied, an electrically conductive fluid, such as blood, a blood product, a medical fluid or the like flows between the patient and a fluid system via a single access device. Dislodgment detection of a single access device can include, for example, the detection of needle dislodgment during the delivery of any suitable and electrically conductive fluid or fluids including, for example, blood or medical drug or solution (i.e., a medication contained in an electrically conductive fluid, such as saline), processed blood, blood products, intravenous solutions, the like or combinations thereof. The fluid delivery can be made between a suitable container, such as blood bags or like fluid delivery devices, and a patient. In this regard, immediate and responsive detection of access disconnection via the present invention can be effectively utilized to monitor and control the transfer of blood or a medical fluid, such as a medication or drug, during medical therapy administered via a single needle.[0073]
• As shown in FIG. 1C, an embodiment of the apparatus or[0074]device54 of the present invention includes anaccess device56; such as a needle, inserted into ablood vessel58 within aneedle insertion site60 of thepatient62. Theneedle56 is connected to thefluid system63, such as a fluid infusion system, via atube member64. The infusion system includes, for example, aninfusion pump66 for transferring the blood or the like from a container68 (e.g., blood bag) to the patient. A firstelectrical contact70 is spaced apart from theneedle56 along thetube member64 and a secondelectrical contact72 is attached to the patient near theinsertion site60. The firstelectrical contact70 is in fluid contact with the fluid as it flows from thedelivery container68 to the patient.
• In this configuration, the first and second electrical contacts, preferably electrodes, can be used to monitor changes in an electrical value, preferably impedance, within a conductor loop formed by at least a portion of the fluid circuit as an electric signal passes therein. In an embodiment, at least one of the electrical contacts can include a conductive polymer material as described below in greater detail. The electrical contact points can be coupled to an[0075]electronic device74 which is capable of processing a detectable signal transmitted through the electrodes in response to a change in impedance or the like due to dislodgment of the single access device as described in detail below. Preferably, the electrical signal is generated by a constant current supplied to the electrodes such that a direct conductivity measurement can be conducted to detect a change in impedance or the like in response to changes in vascular access conditions, such as dislodgment of the access needle.
• It is believed that the measured impedance, in the single needle application, is a function of both the impedance of the fluid (i.e., blood) and the impedance as measured across the insertion site. In this regard, the[0076]electronic device74 can be adjusted to detect the impedance at the level equivalent to the combined impedance of all items of the electrical path (i.e., the conductive fluid in the tube, needle, blood stream of venous vessel, body tissue, impedance across the skin with respect to thesensing electrode72 and the like).
Electrical Contacts
• As previously discussed, the electrical contacts of the present invention are in fluid contact with the fluid as it flows through the fluid circuit. In this regard, the electrical contacts can be utilized to monitor changes in conditions associated with patient therapy. For example, the electrical contacts allow for a direct conductivity measurement which is capable of immediately detecting, with high sensitivity and specificity, a change (e.g., an increase) in impedance or the like due to access disconnection, such as dislodgment of a venous needle (arterial needle or both) from the blood circuit during dialysis therapy. Other types of monitoring applications include monitoring conductivity changes in response to solution compounding as described below in greater detail. It should be appreciated that the present invention can be utilized to monitor one or a combination of condition changes.[0077]
• The electrical contacts can be composed of any suitable conductive and biocompatible material, such as, any suitable electrode material including stainless steel, other suitable conductive materials or combinations thereof. It is essential that the electrode material is biocompatible. In an embodiment, the electrical contact includes a conductive polymer material as described below in greater detail.[0078]
• It should be appreciated that the electrical contacts can be constructed in a variety of different shapes and sizes, illustrative examples of which are described below. For example, the electrical contacts can be configured or designed as a plaster electrode which includes an agent capable of expanding when in contact with moisture. The agent can include a variety of suitable materials including gels that are known to expand more than ten times in volume upon contact with moisture.[0079]
• In an embodiment, the plaster electrode can be utilized to detect fluid (i.e., blood leakage) at an insertion site of an access device insertable within a patient during the administration of medical therapy via a single access device as previously discussed. Upon contact with the fluid, the plaster electrode would necessarily expand to such an extent that the electrode contact is broken, thus causing a detectable increase in impedance of the fluid as it flows from the fluid system to the patient via the needle.[0080]
• In an embodiment, one or more electrodes (not shown), such as one or more plaster electrodes as previously discussed, can be used in combination with the electrical contact pair as shown, for example, in FIGS. 1A and 1B. For example, a plaster electrode can be attached to the patient near the insertion site of either or both of the arterial and venous needles. In this regard, the plaster electrode(s) can be utilized to detect leakage of fluid, such as blood, from the insertion site of the access device(s).[0081]
• In an embodiment, an electrode pair is coupled to the blood circuit in an invasive manner (illustrated in FIGS. 2A-2C as discussed below) such that the electrodes contact the blood as previously discussed. An excitation source that includes a constant current source or the like can be applied to the electrodes to inject an electric signal into the blood circuit thereby defining a conductor loop along which direct conductivity measurements can be performed.[0082]
• To ensure patient safety, the excitation source is typically isolated from the instrument power. Preferably, the excitation source produces a constant electrical current that passes through the blood via the electrodes. Any suitable amount of current can be generated for detection purposes. In an embodiment, the electrical current as it passes through the blood is maintained at a level of about 10 microamperes or less, preferably about[0083]5 microamperes or less. It should be appreciated that the present invention can be operated at low levels of current (e.g., 10 microamperes or less) such that the level of current has negligible, if any, effect on the health and safety of the patient.
• It should be appreciated that the impedance or other suitable parameter can be measured and calculated in a variety of different and suitable ways. For example, the amplitude, phase and/or frequency of the constant current excitation source can be measured and varied during the detection of a change in impedance. Impedance levels can then be detected by measuring the voltage across the electrodes In this regard, the amplitude, frequency and/or phase of the voltage can then be measured and utilized in combination with the measured amplitude, frequency and/or phase of the excitation source to calculate blood impedance levels based on derivations or equations which are typically used to calculate impedance.[0084]
• The electrical contacts can be connected to the blood circuit in a variety of different and suitable ways. For example, the electrical contacts can be an integral component of the extracorporeal system, a disposable component that can be connected and released from the tubing members of the blood circuit, a reusable component that can be autoclaved between uses, or the like.[0085]
Electrical Contact Coupling Device
• In an embodiment, the apparatus of the present invention includes an electrical contact coupling device that can be utilized to secure the electrical contacts, preferably electrodes, to the blood circuit such that the electrodes effectively contact the blood and, thus, can be used to effectively monitor changes in access conditions as previously discussed. In an embodiment, at least one of the electrical contacts includes a conductive polymer material as described below. The coupling device of the present invention can also be designed to facilitate the protection of the user against contact with potential electrical sources. In an embodiment, the device can include a conductive element connected to a tube, through which a medical fluid can flow wherein the conductive element has a first portion exposed to the medical fluid, such as blood, and a second portion external to the tube.[0086]
• The coupling device of the present invention can include a variety of different and suitable configurations, components, material make-up or the like. In an embodiment, the present invention can include a device for connecting an electrical contact to a fluid conduit providing fluid and electrical communication between the electrical contact and fluid flowing through the fluid conduit. The device can include a first member including an annular portion capable of accommodating the electrical contact and a first stem portion connected to the annular member wherein the stem portion has an opening extending therethrough to the annular portion; a second member including a base portion with a groove region and a second stem portion with an opening extending therethrough to the groove region allowing the first member to be inserted and secured to the second member; and a contact member adapted to fit the first and second stem portions allowing the contact member to abut against at least a portion of the electrical contact member allowing an electrical connection to be made between the electrical contact and the contact member. Illustrative examples of the electrical contact coupling device of the present invention are described below.[0087]
• As illustrated in FIGS. 2A and 2B, the electrical[0088]contact coupling device80 includes aprobe member82 that has a cylindrical shape with anopening84 extending therethrough. In this regard, an electrical contact, preferably anelectrode86 having a cylindrical shape can be inserted into theopening84 such that theelectrode86 is secure within theprobe member82. In an embodiment, theprobe member82 has achannel85 extending along at least a portion of theopening84 within which theelectrode86 can be inserted into theprobe member82. A tube member, for example, from a blood tubing set, connector tube member of a dialysis machine or the like, can be inserted into both ends of theopening84 of theprobe member82 in contact with an outer portion of thechannel85 allowing blood or other suitable fluid to make fluid contact with theelectrode86 in any suitable manner. Theelectrode86 has anopening88 that extends therethrough within which blood (not shown) or other suitable fluid from the fluid circuit can flow. In an embodiment, the diameter of theopening88 of theelectrode86 is sized to allow blood flow through theelectrode86 such that blood flow levels under typical operating conditions, such as during dialysis therapy, can be suitably maintained. In this regard, the coupling device of the present invention can be readily and effectively attached to a fluid circuit, including a blood circuit or the like, for use during medical therapy including, for example, dialysis therapy. It should be appreciated that thecoupling device80 of the present invention can be attached to the fluid circuit in any suitable way such that electrical and fluid connection can be made with the fluid flowing through the fluid circuit.
• The[0089]probe member82 also includes astem portion90 that extends from asurface92 of its cylindrical-shaped body. Thestem portion90 has anopening93 that extends therethrough. In an embodiment, thestem portion90 is positioned such that at least a portion of theelectrode86 is in contact with theopening93 of thestem portion90.
• In order to secure the[0090]electrode86 to the blood circuit, thecoupling device80 includes asocket member94 that includes abody portion96 with anopening98 for accepting theprobe member82 and for accepting a blood tube member (not shown) of the blood circuit such that blood directly contacts the electrode as it circulates through the blood circuit during dialysis therapy. In an embodiment, thesocket member94 includes astem portion100 extending from thebody member96 wherein thestem portion100 includes anopening102 extending therethrough. As theprobe member82 is inserted through theopening98 of thebody member96, thestem portion90 of theprobe member82 can be inserted into theopening102 of thestem portion100 of thebody96 of thesocket member94.
• In an embodiment, the[0091]socket member94 includes agroove region104 extending along at least a portion of thebody96 of thesocket member94. In this regard, theprobe member82 can be inserted through theopening98 and then moved or positioned into thegroove region104 to secure theprobe member82 within thebody96 of thesocket member94.
• In an embodiment, the[0092]coupling device80 includes anelectrical contact member106 that is inserted within theopening102 of thestem portion100 of thebody96 of thesocket member94 such that theelectrical contact member106 extends through theopening93 of thestem portion90 of theprobe member82 to contact at least a portion of asurface108 of theelectrode86.
• The[0093]electrical contact member106 is utilized to connect the electronics (not shown) of, for example, the excitation source, a signal processing device, other like electronic devices suitable for use in monitoring and/or controlling changes in access conditions, such as needle dislodgment. Theelectrical contact member106 can be made of any suitable material, such as any suitable conductive material including, stainless steel, other like conductive materials or combinations thereof. In order to secure theelectrical contact member106 in place, acontact retainer member110 is inserted within theopening102 of thestem portion100 at anend region112 thereof.
• In an embodiment, the coupling device is mounted to a dialysis machine, device or system in any suitable manner. For example, the coupling device can be mounted as an integral component of the dialysis machine. As well, the coupling device can be mounted as a separate and/or stand alone component which can interface with any of the components of the apparatus and system of the present invention. In an embodiment, the[0094]coupling device80 can be insertably mounted via thestem portion100 of thesocket member94 to a dialysis machine or other suitable components.
• It should be appreciated that the electrical contact coupling device can include a variety of different and suitable shapes, sizes and material components. For example, another embodiment of the coupling device is illustrated in FIG. 2C. The[0095]coupling device114 in FIG. 2C is similar in construction to the coupling device as shown in FIGS. 2A and 2B. In this regard, thecoupling device114 of FIG. 2C can include, for example, a cylindrical-shaped electrode or other suitable electrical contact, a probe member for accepting the electrode and securing it in place within a socket member of the sensing device. The probe member includes a stem portion that is insertable within a stem portion of the socket member. An electrical contact member is insertable within the stem portion such that it can contact the electrode. The coupling device of FIG. 2C can also include a contact retainer member to hold the electrical contact member in place similar to the coupling device as shown in FIGS. 2A and 2B.
• As shown in FIG. 2C, the[0096]probe member116 of the electricalcontact coupling device114 includes ahandle118 which can facilitate securing theprobe member116 within thesocket member120. Thehandle118, as shown, has a solid shape which can facilitate the use and manufacture of thecoupling device114. In addition, the stem portion (not shown) of theprobe member116 is larger in diameter than the stem portion of the probe member as illustrated in FIG. 2A. By increasing the stem size, the probe member can be more easily and readily inserted within the socket member. Further, the probe member is greater in length as compared to the probe-member as shown in FIGS. 2A and 2B such that theend regions122 of theprobe member116 extend beyond agroove region124 of thesocket member120. This can facilitate securing the probe member within thegroove region124 of thesocket member120.
• In an embodiment, an[0097]opening126 of thesocket member120 can include anadditional opening portion128 to accommodate the insertion of the stem portion of theprobe member116, having an increased size, therethrough. This can ensure proper alignment of the probe member with respect to the socket member before insertion of the probe member into the socket member thus facilitating the insertion process.
• It should be appreciated that the probe member, socket member and contact retainer member can be composed of a variety of different and suitable materials including, for example, plastics, molded plastics, like materials or combinations thereof. The various components of the coupling device, such as the probe member, socket member and contact retainer member, can be fitted in any suitable way. For example, the components can be fitted in smooth engagement (as shown in FIGS. 2A and 2B), in threaded engagement (as shown in FIGS. 2D and 2E) and/or any suitable fitting engagement or arrangement to one another.[0098]
• As shown in FIGS. 2D and 2E, the[0099]coupling device130 of the present invention can be made of threaded parts which are removably connected to one another to form the coupling device. The threaded parts can facilitate securing the electrode to the blood circuit as well as general use of same as described below.
• In an embodiment, the[0100]stem portion132 of thebody134 of thecoupling device130 has a threadedregion136 which can be insertably attached to a dialysis machine or other suitable mounting device in threaded engagement. This can facilitate the ease in which the coupling device is attached and detached from the mounting device.
• As shown in FIG. 2E, the[0101]stem portion132 is threaded on both sides allowing it to be in threaded engagement with anannular member138. Theannular member138 provides direction and support allowing theelectrical contact member140 to abut against theelectrode142 housed in theprobe member144 as previously discussed.
• In an embodiment, a[0102]plate member146 made of any suitable conductive material can be depressed against aspring148 as theprobe member144 is secured to thebody134. At the same time, anotherspring150 can be displaced against theelectrical contact member140 in contact with theretainer152 which is inserted within an annular region of theannular member138 to secure theelectrical contact member140 to thebody134.
• The spring mechanism in an embodiment of the present invention allows the parts of the[0103]coupling device130 to remain in secure engagement during use. It can also facilitate use during detachment of the parts for cleaning, maintenance or other suitable purpose.
• As previously discussed, the present invention can be effectively utilized to detect dislodgment of an access device, such as a needle, inserted within a patient through which fluid can pass between the patient and a fluid delivery and/or treatment system. The present invention can be applied in a number of different applications, such as medical therapies or treatments, particularly dialysis therapies. In dialysis therapies, access devices, such as needles, are inserted into a patient's arteries and veins to connect blood flow to and from the dialysis machine.[0104]
• Under these circumstances, if the needle becomes dislodged or separated from the blood circuit, particularly the venous needle, the amount of blood loss from the patient can be significant and immediate. In this regard, the present invention can be utilized to controllably and effectively minimize blood loss from a patient due to dislodgment of the access device, such as during dialysis therapy including hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement.[0105]
Signal Detection and Processing
• As previously discussed, the electrical contacts in connection with the controller can be used to detect a change in impedance or the like in response to needle drop-out or other like changes in access conditions. The electrical contacts can include a variety of suitable conductive materials, such as conductive polymer materials as described below. In an embodiment, the present invention can be adapted to correct for any variations in the baseline impedance over time. This can increase the level of sensitivity with respect to the detection capabilities of the present invention. In this regard, if changes in the baseline impedance are too great and not adequately corrected for, changes in impedance due to needle dislodgment may not be as readily, if at all, detectable above baseline values.[0106]
• From a practical standpoint, there are a number of different process conditions that may influence a change in the baseline impedance over time. For example, a gradual drift or change in the baseline can occur due to a change in the characteristics, such as the hematocrit, plasma protein, blood/water conductivity and/or the like, of the blood or other suitable fluid during treatment. This can arise due to changes in the level of electrolytes or other components during dialysis therapy.[0107]
• As illustrated in FIG. 3, the present invention can process a measurable voltage signal to correct for changes in baseline impedance over time. This can enhance the detection capabilities of the present invention as previously discussed. In an embodiment, a[0108]current source160 or the like generates an electric current to pass through the blood as it circulates into, through and out of the patient along theextracorporeal blood circuit162 which connects the patient via venous and arterial needles to the dialysis system including a variety of process components. The electric current is injected into the blood circuit via a firstelectrical contact163athereby defining a conductor loop or pathway along the blood circuits. Preferably, the current is maintained at a constant level until dislodgment occurs. Thesecond electrode163bis used to sense voltage or the like along the conductor loop and then pass a signal indicative of same and/or changes thereof to an electronic device for detection and processing as previously discussed. The voltage signal can be measured and processed in any suitable manner.
• In an embodiment, the signal is passed through a series of components including a filter or[0109]filters164 which can act to filter noise from the signal, particularly noise derived from the rotation from the pump in order to minimize a false negative and/or positive detection of needle dislodgment, arectifier166, apeak detector168 and an analog to digital converter (“ADC”)170 to digitize the signal. In this regard, the digital signal can then be stored in a computer device (not shown) for further processing. The voltage signal is continually measured and processed over time. With each measurement, the digitized signals are compared to evaluate changes due to baseline changes associated with variations in process conditions over time, such as a change in the characteristics of blood as previously discussed. If a baseline change is determined, the digitized signal can be further processed to correct for the change in baseline.
• The voltage data is continually sent to a[0110]control unit172 coupled to the ADC. The control unit continually performs a calculation to determine whether a change in impedance or the like in response to needle dislodgment has occurred. In an embodiment, dislodgment of an access device is detected when [V(t)−V(t−T)]>C1, where t is time, where T is the period of blood pump revolution, where C1 is a constant and where V(t)=I_o*Z, where I_ois current and where Z is the impedance of the bloodline which is a function of the impedance associated with patient's vascular access and the impedance associated with various components of the dialysis system, such as the dialyzer, as previously discussed.
• If disconnection of the patient from the blood circuit is detected, the[0111]control unit172 can be utilized to process the signal in order to minimize blood loss from the patient. In an embodiment, the controller is in communication with a dialysis system as applied to administer dialysis therapy including, for example, hemodialysis, hemofiltration, hemodiafiltration and continuous renal replacement. This communication can be either hard-wired (i.e., electrical communication cable), a wireless communication (i.e., wireless RF interface), a pneumatic interface or the like. In this regard, the controller can process the signal to communicate with the dialysis system or device to shut off or stop theblood pump174 associated with the hemodialysis machine and thus effectively minimize the amount of blood loss from the patient due to needle dislodgment during hemodialysis.
• The controller can communicate with the dialysis system in a variety of other ways. For example, the controller and hemodialysis machine can communicate to activate a[0112]venous line clamp176 for preventing further blood flow via the venous needle thus minimizing blood loss to the patient. In an embodiment, the venous line clamp is activated by the controller and attached to or positioned relative to the venous needle such that it can clamp off the venous line in close proximity to the needle. Once clamped, the dialysis system is capable of sensing an increase in pressure and can be programmed to shut-off the blood pump upon sensing pressure within the blood flow line which is above a predetermined level. Alternatively, the venous line clamp can be controllably attached to the dialysis system.
• In an embodiment, an alarm can be activated upon detection of blood loss due to, for example, needle dislodgment during dialysis therapy. Once activated, the alarm (i.e., audio and/or visual or the like) is capable of alerting the patient, a medical care provider (i.e., doctor, registered nurse or the like) and/or a non-medical care provider (i.e., family member, friend or the like) of the blood loss due to, for example, needle dislodgment. The alarm function is particularly desirable during dialysis therapy in a non-medical facility, such as in a home setting or self care setting where dialysis therapy is typically administered by the patient and/or a non-medical care provider in a non-medical setting or environment excluding a hospital or other like medical facility.[0113]
• In this regard, the alarm activation allows, for example, the patient to responsively act to ensure that the dialysis therapy is terminated by, for example, to check that the blood pump has been automatically shut off to minimize blood loss to the patient. Thus, the patient has the ability to act without the assistance of a third party (i.e., to act on his or her own) to ensure that responsive measures are taken to minimize blood loss. The alarm can thus function to ensure the patient's safety during the administration of dialysis therapy, particularly as applied to home hemo treatments where at least a portion of the dialysis therapy can be administered while the patient is sleeping.[0114]
Dialysis Machine
• As previously discussed, the present invention can be adapted for use with any suitable fluid delivery system, treatment system or the like. In an embodiment, the present invention is adapted for use with a dialysis machine to detect access disconnection as blood flows between the patient and the dialysis machine along a blood circuit during treatment, including, for example hemodialysis, hemofiltration and hemodiafiltration.[0115]
• The present invention can include any suitable dialysis machine for such purposes. An example, of a hemodialysis machine of the present invention is disclosed in U.S. Pat. No. 6,143,181 herein incorporated by reference. In an embodiment, the[0116]dialysis machine190 includes amobile chassis192 and it has at thefront side194 thereof acommon mechanism196 for connecting tubing or the like by which a patient can be connected to the dialysis machine as shown in FIG. 4B. Aflat touch screen197 which can show several operational parameters and is provided with symbols and fields for adjustment of the dialysis machine by relevant symbols and fields, respectively, on the screen being touched can be adjusted vertically and can be universally pivoted on the dialysis machine and can be fixed in the desired adjusted position.
• In an embodiment, the dialysis machine includes a chassis having one or more connectors for connecting a patient to the dialysis machine via a blood circuit allowing blood to flow between the patient and the dialysis machine during dialysis therapy wherein one or more electrical contacts are connected to the blood circuit in fluid communication with the blood allowing detection of a change in an electrical value in response to access disconnection as the blood flows through the blood circuit having an electrical signal passing therein.[0117]
• In an embodiment, the dialysis machine of the present invention can be designed to accommodate one or more of the electrical contact coupling devices, such as a pair of coupling device, used to detect access disconnection as shown in FIG. 4B. For example, one or[0118]more coupling devices198 can be attached to thefront panel194 of thedialysis machine190. This can be done in any suitable way. In an embodiment, the a stem portion of the coupling device is insertably mounted via- a threaded fit, frictional fit or the like, as previously discussed. This connects the patient to thedialysis machine190 via a blood tubing set202. The blood tubing set includes afirst blood line204 and asecond blood line206. In an embodiment, thefirst blood line204 is connected to the patient via anarterial needle208 or the like through which blood can flow from thepatient200 to thedialysis machine190. Thesecond blood line206 is then connected to thepatient200 via avenous needle210 or the like through which fluid flows from the dialysis machine to the patient thereby defining a blood circuit. Alternatively, the first blood line and the second blood line can be coupled to the venous needle and the arterial needle, respectively. The blood lines are made from any suitable medical grade material. In this regard, access disconnection, such as dislodgment of an arterial needle and/or a venous needle can be detected as previously discussed. Alternatively, the coupling device can be attached to the blood tubing set which is then attached to the dialysis machine in any suitable way.
Dialysis Treatment Centers
• As previously discussed, the present invention can be used during dialysis therapy conducted at home and in dialysis treatment centers. The dialysis treatment centers can provide dialysis therapy to a number of patients. In this regard, the treatment centers include a number of dialysis machines to accommodate patient demands. The therapy sessions at dialysis treatment centers can be performed 24 hours a day, seven days a week depending on the locale and the patient demand for use.[0119]
• In an embodiment, the dialysis treatment centers are provided with the capability to detect access disconnection during dialysis therapy pursuant to an embodiment of the present invention. For example, one or more of the dialysis machines can be adapted for use with an electrical contact coupling device along with the necessary other components to detect access disconnection as previously discussed.[0120]
• In an embodiment, the electrical contact coupling device can be directly attached to one or more of the dialysis machines of the dialysis treatment center. It should be appreciated that the apparatuses, devices, methods and/or systems pursuant to an embodiment of the present invention can be applied for use during dialysis therapy administered to one or more patients in the dialysis treatment center in any suitable way. In an embodiment, the treatment center can have one or more patient stations at which dialysis therapy can be performed on one or more patients each coupled to a respective dialysis machine. Any suitable in-center therapy can be performed including, for example, hemodialysis, hemofiltration and hemodiafiltration and combinations thereof. As used herein, the term “patient station” or other like terms mean any suitably defined area of the dialysis treatment center dedicated for use during dialysis therapy. The patient station can include any number and type of suitable equipment necessary to administer dialysis therapy.[0121]
• In an embodiment, the dialysis treatment center includes a number of patient stations each at which dialysis therapy can be administered to one or more patients; and one or more dialysis machines located at a respective patient station. One or more of the dialysis machines can include a chassis having one or more connectors for connecting a patient to the dialysis machine via a blood circuit allowing blood to flow between the patient and the dialysis machine during dialysis therapy wherein a pair of electrical contacts are connected to the blood circuit in fluid communication with the blood allowing detection of a change in an electrical value in response to access disconnection as the blood flows through the blood circuit having an electrical signal passing therein.[0122]
• As previously discussed, the access disconnection detection capabilities of the present invention can be utilized to monitor and control a safe and effective dialysis therapy. Upon dislodgment of an access device, such as a needle, from the patient, the direct conductive measurement capabilities of the present invention can be used to provide a signal indicative of dislodgment that can be further processed for control and/or monitoring purposes. In an embodiment, the signal can be further processed to automatically terminate dialysis therapy to minimize blood loss due to dislodgment as previously discussed. Further, the signal can be processed to activate an alarm which can alert the patient and/or medical personnel to the dislodgment condition to ensure that responsive measures are taken. It should be appreciated that the present invention can be modified in a variety of suitable ways to facilitate the safe and effective administration of medical therapy, including dialysis therapy.[0123]
• Applicants have found that the direct conductive measurement capabilities of the apparatus of the present invention can immediately detect blood loss or the like due to access disconnection, such as needle dislodgment, with high sensitivity and selectivity such that responsive measures can be taken to minimize blood loss due to same. The ability to act responsively and quickly to minimize blood loss upon detection thereof is particularly important with respect to needle dislodgment during hemodialysis. If not detected and responded to immediately, the amount of blood loss can be significant. In an embodiment, the present invention is capable of taking active or responsive measures, to minimize blood loss (i.e., shut-off blood pump, activate venous line clamp, activate alarm and/or the like) within about three seconds or less, preferably within about two to about three second upon immediate detection of needle dislodgment.[0124]
• In addition, the controller can be utilized to monitor and/or control one or more treatment parameters during hemodialysis. These parameters can include, for example, the detection of blood due to blood loss upon needle dislodgment, the change in blood flow, the detection of air bubbles in the arterial line, detection of movement of the sensor during treatment, detection and/or monitoring of electrical continuity of the sensor or other like treatment parameters. In an embodiment, the controller includes a display (not shown) for monitoring one or more of the parameters. Thus, the present invention can be utilized to promote the safe and effective administration on patient therapy, such as dialysis therapy, as previously discussed.[0125]
• As used herein “medical care provider” or other like terms including, for example, “medical care personnel”, means an individual or individuals who are medically licensed, trained, experienced and/or otherwise qualified to practice and/or administer medical procedures including, for example, dialysis therapy, to a patient. Examples of a medical care provider include a doctor, a physician, a registered nurse or other like medical care personnel.[0126]
• As used herein “non-medical care provider” or other like terms including, for example, “non-medical care personnel” means an individual or individuals who are not generally recognized as typical medical care providers, such as doctors, physicians, registered nurses or the like. Examples of non-medical care providers include patients, family members, friends or other like individuals.[0127]
• As used herein “medical facility” or other like terms including, for example, “medical setting” means a facility or center where medical procedures or therapies, including dialysis therapies, are typically performed under the care of medical care personnel. Examples of medical facilities include hospitals, medical treatment facilities, such as dialysis treatment facilities, dialysis treatment centers, hemodialysis centers or the like.[0128]
• As used herein “non-medical facility” or other like terms including, for example, “non-medical setting” means a facility, center, setting and/or environment that is not recognized as a typical medical facility, such as a hospital or the like. Examples of non-medical settings include a home, a residence or the like.[0129]
• It should be appreciated that the electrode output signal can be combined with other less sensitive blood loss detection methods, such as venous pressure measurements, systemic blood pressure, the like or combinations thereof, to improve specificity to needle dislodgment.[0130]
Conductive Polymer
• As previously discussed, the present invention provides conductive polymer materials and devices, apparatuses, systems and methods that employ same. The conductive polymer material can be utilized in a number of different applications, such as to monitor patient therapy. For example, the conductive polymer materials can be utilized to monitor patient access conditions as discussed above and as further detailed below. Other types of monitoring applications include, for example, monitoring solution mixing or compounding as described in greater detail below. The present invention contemplates monitoring one or a combination of condition changes associated with patient therapy, such as monitoring patient access conditions and solution mixing conditions, alone or in combination.[0131]
• In an embodiment, the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix. Alternatively, the conductive polymer material, in an embodiment, includes a conductive polymer component without a separate conductive component, such as stainless steel. It should be appreciated that the conductive polymer material can be made from any suitable types and amounts of materials and in any suitable way.[0132]
• As discussed above, the conductive polymer can include a polymer matrix and a conductive component incorporated in the matrix. The polymer matrix can include a variety of different polymer-based materials that are suitable for use in a variety of applications, particularly including medical applications, such as dialysis therapy. In an embodiment, the polymer matrix includes polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene, like polymeric materials and suitable combinations thereof.[0133]
• The conductive component can include any suitable material or combination of materials that have conductive properties applicable for a number of different applications including, for example, detecting patient access disconnection during medical therapy as previously discussed, monitoring the mixing or compounding of solution components to form a mixed solution, and/or other like applications. Preferably, the conductive component includes stainless steel, fillers, carbon black, fibers thereof and/or the like.[0134]
• The conductive component can be sized and shaped in any suitable way such that it can be readily incorporated in the polymer matrix. For example, the conductive component can include conductive fibers made from any suitable material, such as stainless steel, a carbonaceous material and/or the like. The fibers, in an embodiment, have an aspect ratio that ranges from about 2:1 to about 30:1.[0135]
• The conductive polymer material can include any suitable amount of the conductive polymer matrix and the conductive component. This can vary depending on the application of the conductive polymer material. In an embodiment, the conductive component includes greater than about 10% by weight of the conductive polymer material. Preferably, the conductive component ranges from about 10% to about 50% by weight of the conductive polymer material. It should be appreciated that more than about 50% by weight of the conductive component can be utilized but may provide minimal, if any, increase in performance of the conductive polymer material depending on the application. Preferably, the conductive component is uniformly dispersed throughout the polymer matrix.[0136]
• As previously discussed, the conductive polymer material, in an embodiment, is composed of a conductive polymer component. This type of component has sufficient electrical conductivity properties such that an additional conductive component, such as stainless steel, is not required. Examples of conductive polymer material components include polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene), the like and mixtures thereof.[0137]
• As previously discussed, the conductive polymer material can be made in any suitable way. In general, the conductive component is mixed with the polymer component under suitable processing conditions including temperature and pressure, for example, to form a polymer matrix with the conductive component incorporated therein. The mixing should take place over a suitable period of time and with a sufficient amount of force such that the conductive component is uniformly distributed throughout the polymer matrix.[0138]
• The polymer matrix incorporated with a conductive component is then shaped and formed into a final product in any suitable way. For example, the polymer matrix incorporated with the conductive component can be formed into a single piece part via an injection molding process, extrusion process or the like under suitable processing conditions. Thus, the conductive polymer material can be readily made with manufacturing techniques, such as injection molding and extrusion. This can effectively provide a cost savings to the manufacturing process that can be inevitably passed along to the consumer.[0139]
• The conductive polymer material can be formed into any suitable shape and size depending on the application. In an embodiment, the conductive polymer material is formed into an electrode or other like electrical contact that can be utilized for a number of different applications, including, for example, monitoring patient access conditions and/or monitoring solution mixing or compounding as discussed above and described below in greater detail. The conductive polymer electrode can have a variety of different and suitable configurations depending on the application. For example, the conductive polymer electrode can be made into a coupler that can be used to join tubing to form a tubing joint as described below.[0140]
• As shown in FIGS. 5A and 5B, the conductive polymer coupler has a generally cylindrical shape. With this configuration, the conductive polymer can be readily attached to a tube through which fluid flows, thus forming a tubing joint.[0141]
• As shown in FIG. 5A, the[0142]coupler220 has amember222 that extends from aninner surface224 of thecoupler electrode220. Themember222 acts as a stop for thetube226 that is attached to the electrode such that a desired length of the tubing joint228 can be preset. Thecoupler220 as shown in FIG. 5A, in an embodiment, is made via an injection molding process.
• As shown in FIG. 5A, a first tube member[0143]230 is attached to a first end232 of thecoupler220 and positioned or stopped by afirst end234 of themember222. Asecond tube member236 is attached to asecond end238 of thecoupler220 and stopped or positioned by asecond end240 of themember222. This forms a tubing joint228, such as a tubing joint that is integrated within a blood circuit and utilized during dialysis therapy as described in the present application.
• As shown in FIG. 5B, the[0144]coupler242 is formed without a member that allows the length of the tubing joint to be preset as discussed above. In this regard, the tubing joint length can be adjusted accordingly depending on the application. Further, thecoupler242 as shown in FIG. 5B can be made via an extrusion process instead of an injection molding process. This can provide a further cost savings with respect to manufacturing of the coupler as compared to an injection molding process as discussed above. As shown in FIG. 5B, afirst tube member244 is attached to afirst end246 of thecoupler242 and asecond tube member248 is attached to thesecond end250 of thecoupler242, thus forming thetubing joint252.
• The tube member can be attached to the conductive polymer coupler in any suitable way. For example, the conductive polymer material can be solvent bonded, heat sealed, laser welded, radio frequency sealed, or the like to the tubing.[0145]
• The tubing can be made of any suitable material depending on the application. For example, the tubing can be made from polyvinyl chloride (“PVC”). Preferably, the PVC tubing is attached to a conductive polymer material that is made with a polymer matrix composed of acrylonitrile butadiene styrene (“ABS”) where the ABS-based conductive material is solvent bonded to the PVC tubing.[0146]
• However, the tubing can be made of a variety of different materials depending on the application. In an embodiment, the tubing includes a non-PVC material, such as metallocene-based polyethylene polymers, cyclo olefin copolymers, cyclo olefin copolymer blends and the like. The non-PVC materials can include any suitable type and amount of constituents. Metallocene-based polyethylene polymers and the like illustrative of the present invention can be found, for example, in U.S. Pat. No. 6,372,848, the disclosure of which is herein incorporated by reference. These types of non-PVC polymers can include a polymer blend that has a first ethylene and α-olefin copolymer obtained using a single site catalyst present in an amount by weight of from about 0% to about 99% by weight of the blend and having a melt flow index from fractional, such as about 0.1 g/10 min to about 5 g/10 min, a second ethylene and α-olefin copolymer obtained using a single site catalyst and being present in an amount by weight of the blend from about 0% to about 99% and having a melt flow index from higher than about 5 g/10 min to about 20 g/10 min; and a third ethylene and α-olefin copolymer obtained using a single-site catalyst and being present in an amount by weight of the blend from about 0% to about 99% and having a melt flow index greater than about 20 g/10 min. In an embodiment, the α-olefin copolymer has a molecular weight distribution of less than about 3.[0147]
• Cyclo olefin copolymers and blends thereof illustrative of the present invention can be found, for example, in U.S. Pat. No. 6,255,396, the disclosure of which is herein incorporated by reference. These types of non-PVC polymers can include as a component homopolymers or copolymers of cyclic olefins or bridged polycyclic hydrocarbons. For example, the polymer composition includes a first component obtained by copolymerizing a norbomene monomer and an ethylene monomer wherein the first component is in an amount from about 1-99% weight of the composition; and a second component of an ethylene and α-olefin copolymer that has six carbons wherein the second component is in an amount from about 99% to about 1% by weight of the composition. In an embodiment, the polymer composition can include an additional component, such as a second homopolymer or copolymer of a cyclic olefin or a bridged polycyclic hydrocarbon.[0148]
• The non-PVC based tubing and the non-PVC based conductive coupler can be joined in any suitable way to form a tubing joint. In an embodiment, the non-PVC based tubing and coupler are joined via solvent bonding, such as disclosed in U.S. Pat. Nos. 6,255,396 and 6,372,848. As used herein the term solvent bonding or other like terms means that the tubing can be exposed to a solvent to melt, dissolve or swell the tubing and then be attached to another polymeric component to form a permanent bond. Suitable solvents typically include those having a solubility parameter of less than about 20 (Mpa)[0149]^1/2. Suitable solvents can also have a molecular weight less than about 200 g/mole. The solvent can include, for example, aliphatic hydrocarbons, aromatic hydrocarbons, and mixtures thereof. As used herein, the terms aliphatic hydrocarbon and aromatic hydrocarbon are compounds containing only carbon and hydrogen atoms.
• Suitable aliphatic hydrocarbons can include substituted and unsubstituted hexane, heptane, cyclohexane, cycloheptane, decalin and the like. Suitable aromatic hydrocarbons can include substituted and unsubstituted aromatic hydrocarbon solvents, such as xylene, tetralin, toluene, cumene and the like. Suitable hydrocarbon substituents can include aliphatic substituents that have from 1-12 carbons and include propyl, ethyl, butyl, hexyl, tertiary butyl, isobutyl, the like and combinations thereof.[0150]
• As previously discussed, the conductive polymer of the present invention can be constructed and arranged into a variety of different configurations, such as a conductive polymer coupler as shown in FIGS. 5A and 5B and discussed above. Another example includes a dialyzer header that is made from the conductive polymer according to an embodiment. Referring to FIG. 6, a[0151]dialyzer253 is generally illustrated. Thedialyzer253 includes abody member254 that generally includes acasing256. Thecasing256 includes a core section as well as twobell members260 located at each end of the dialyzer. Located within the core is afiber bundle258. The dialyzer also includes adialysate inlet262 and adialysate outlet264.
• Located at a[0152]first end266 of thedialyzer253 is afluid inlet268 and at asecond end270 is afluid outlet272 defined by afluid inlet header274 and afluid outlet header276, respectively. Thedialyzer253 is connected to a dialysis blood circuit in any suitable manner. In an embodiment, theinlet274 andoutlet276 headers are made from the conductive polymer material of the present invention as discussed above. Theinlet274 andoutlet276 headers can be connected to acontroller278 such that the conductive polymer headers can be utilized to monitor patient access conditions as previously discussed.
• A variety of different header and dialyzer designs can be utilized. For example, U.S. Pat. No. 6,623,638 and U.S. Patent Publication No. 2003/0075498 provide a number of different examples illustrative of the present invention. The disclosures of U.S. Pat. No. 6,623,638 and U.S. Patent Publication No. 2003/0075498 are herein incorporated by reference.[0153]
• The conductive polymer of the present invention can be utilized in any suitable way and in a variety of different devices, apparatuses, systems and applications thereof. For example, the conductive polymer can be utilized to detect a change in impedance in response to dislodgement of an access device, to detect a change in conductivity in response to a change in solution composition and/or other suitable applications.[0154]
• In an embodiment, the conductive polymer is part of a sensor assembly or apparatus that can be utilized, for example, for monitoring dialysis applications as discussed in the present application. The sensor apparatus of the present invention can include a number of different configurations and designs. Two examples of such designs illustrative of the present invention are described below in FIGS. 7A and 7B.[0155]
• In FIG. 7A, the tubing joint[0156]284 that includes the conductive polymer electrode286 attached to atube member288 as described above, for example, is positioned in place by a holdingdevice290 or holder for purposes of detection capabilities associated with thesensor apparatus291 in an embodiment. In general, theholder290 as shown in FIG. 7A has a hub design. More specifically, theholder290 includes abase member292 onto which the tubing joint284 can be placed. Thebase member292 includes afirst portion294 that is made from a plastic or other suitable material. Thefirst portion294 defines anouter surface296 of thebase member292. Along theouter surface296, thefirst portion294 includes two openings that are spaced apart as shown in FIG. 7A. Thefirst opening298 is located on afirst edge300 of the first portion of the base and thesecond opening302 is located on a second edge304 of the first portion of the base. The openings can be configured in any suitable way and be utilized for mounting purposes.
• The second portion of the base member includes a[0157]conductive portion306 as shown in FIG. 7A. In an embodiment, theconductive portion306 includes asingle piece part308 that is made from any suitable conductive material, such as stainless steel and/or the like. As shown in FIG. 7A, the conductive polymer of the tubing joint is placed against acurved edge310 of the second portion that substantially forms to anouter surface312 of the conductive polymer electrode286. The electrode is substantially cylindrical in shape.
• The[0158]holder290 further includes anarm member314 that is pivotally attached to thebase member292 as shown in FIG. 7A. Thearm member314 includes a generally curved region such that thearm314 can be positioned over the tubing joint284 allowing it to substantially conform to the generally cylindrical surface of the tube joint and thus further securing the tubing joint284 in place.
• Another configuration of a hub design illustrative of the sensor apparatus of the present invention is shown in FIG. 7B. In general, this design provides a box-[0159]like holder316 that encloses the tubing joint318 wherein the tubing joint includes theconductive polymer electrode320 in the form of a coupler that is attached to thetube member322 as discussed above. Theholder316 includes abase member324. Thebase member324 includesside portions326, abottom portion328 and anopening330 at atop portion332. As shown in FIG. 7B, thesensor apparatus334 includes aconductive member336 that is contained in thebase member324. Theconductive member336 can be made of any suitable material as described above. Theconductive member336 includes an annular-shapedsurface338 against which the tubing joint318 can be placed. Thesensor apparatus334 further includes alid340 that is pivotally attached to thebase member324. Thelid340 has amember342 that abuts against a portion of the tubing joint in a closed position. This secures the tubing joint in place for use.
• As previously discussed, the sensor apparatus of the present application can be used in a number of suitable applications. For example, the sensor apparatus can be suitably coupled to a blood circuit and used for purposes of detecting disconnection of an access device as described in the present application. Another application includes the monitoring of solution compounding as described in greater detail below. In this regard, the sensor apparatus as shown in FIGS. 7A and 7B can be used in combination with or in place of the electrical coupling devices as illustrated in FIGS. 2A-2E and further described above. Thus, the present invention can be utilized to monitor one or a combination of conditions, such as patient access and solution mixing, during use. As applied, the sensor apparatus can be connected to a controller or other like device for detection purposes. The controller can include one or a number of different devices that are in electrical contact with the sensor apparatus in any suitable way.[0160]
• In another embodiment, the sensor apparatus can include a single piece part that is made from the conductive polymer material. The single piece part can be made in any suitable way such as through injection molding as described above. A number of different and suitable shapes and sizes can be formed. One such example illustrative of the present invention of a single piece part[0161]conductive electrode344 is shown in FIGS. 8A and 8B.
• In general, the[0162]conductive polymer electrode344 is configured as a coupler that can join tubing to form a tubing joint through which fluid can flow as shown in FIGS. 8A and 8B. Theconductive polymer electrode344 includes abase member346 that has anannular opening348 extending therethrough. Atube member350 can be attached to theends351 of theannular opening348 such that the tubing joint can be formed as described above. Thebase member346 includes astem portion352 that extends from a portion of asurface354 of thebase member346. This can be used to mount or attach theconductive polymer electrode344 to a control panel or other suitable component, such as a hemodialysis machine as described above. Thestem portion352 defines an annular-shapedchannel356 that ends from thesurface354 of thebase member346. Within the annular-shaped channels, an inner annular-shapedchannel360 is also provided that extends from thesurface354 of thebase346, as shown in FIG. 8B. The stem portion can be utilized to provide a pathway through which the electrode can be in electrical contact with one or more other devices, such as a controller, in any suitable way. The base member further includes atop member362 that extends from a portion of thesurface354 of thebase member346. Thetop member362 can be used to secure thestem portion352 of thebase member346 in place for use and/or to remove the electrode after use.
• As shown in FIGS. 8A and 8B, the[0163]conductive polymer electrode344 includes amember366 that extends from an inner surface of theannular opening348. Themember366 acts as a stop against which the tubing can be placed to form the tubing joint. Themember366 has a generally-cylindrical shape with anopening368 through which fluid can flow.
• As previously discussed, the conductive polymer material of the present invention can be utilized in a number of different applications. In an embodiment, the conductive polymer material can be utilized to monitor patient access conditions, such as to detect disconnection of an access device that is inserted in a patient through which fluid flows during medical therapy. Preferably, the disconnection detection application is applied during dialysis therapy, such as during hemodialysis therapy.[0164]
• As applied to dialysis applications, the conductive polymer can be formed into an electrode and attached to a dialysis blood circuit in any suitable manner. As shown in FIGS. 1A and 2A and further described above, at least one of the sensors can include an electrode made with the conductive polymer material of the present invention. The[0165]sensors22 and24 are in electrical contact with acontroller29 and thus the conductive polymer electrode can be utilized for detection, monitoring and control purposes related to dialysis therapy as described above. As shown in FIGS. 4A and 4B and described in the present application, thesensors198 can be attached directly to the hemodialysis machine wherein at least one of the sensors includes a conductive polymer electrode according to an embodiment of the present invention. The conductive polymer sensor can be configured in any suitable way, such as the coupler and hub design (See, FIGS. 5A, 5B,7A and7B), the single-piece part design (See, FIGS. 8A and 8B) and dialyzer header design (See, FIGS. 8A and 8B) as described above. It should be appreciated that the present invention contemplates the use of one or a combination of different sensors to monitor medical therapy, such as patient access and solution mixing conditions.
• In an embodiment, the conductive polymer material of the present invention can be utilized for monitoring the mixing of solutions to form a mixed solution, such as a mixed solution used during medical therapy. One type of application illustrative of the present invention for such monitoring purposes is during dialysis therapy, particularly during peritoneal dialysis. In general, the conductive polymer material can be formed into an electrode or other sensing device that can effectively detect changes in conductivity associated with a dialysis solution that is administered to the patient during peritoneal dialysis.[0166]
• The dialysis solution can be formed from a number of solution components that are mixed to form a mixed dialysis solution prior to administration. The dialysis solution components can have varying pH levels, such as ranging from about 1.8 to about 9.2. Once mixed, the pH of the mixed dialysis solution should be at a physiologically acceptable level, such as ranging from about 6.8 to about 7.5, prior to use. The pH level can be monitored in relation to changes in the conductivity level of the dialysis solution. In this regard, the conductive polymer of the present invention can be utilized to detect changes in conductivity level and thus can be utilized to determine whether the solution components are properly mixed to form the mixed dialysis solution at an acceptable pH level prior to use. A general description of peritoneal dialysis is provided below and is illustrative of the present invention.[0167]
• Peritoneal dialysis utilizes a sterile dialysis solution, which is infused into a patient's peritoneal cavity and into contact with the patient's peritoneal membrane. Waste, toxins and excess water pass from the patient's bloodstream through the peritoneal membrane and into the dialysis solution. The transfer of waste, toxins, and excess water from the bloodstream into the dialysis solution occurs due to diffusion and osmosis during a dwell period as an osmotic agent in the dialysis solution creates an osmotic gradient across the membrane. The spent solution is later drained from the patient's peritoneal cavity to remove the waste, toxins and excess water from the patient.[0168]
• There are various types of peritoneal dialysis therapies, including continuous ambulatory peritoneal dialysis (“CAPD”) and automated peritoneal dialysis. CAPD is a manual dialysis treatment, in which the patient connects the catheter to a bag of fresh dialysis solution and manually infuses fresh dialysis solution through the catheter or other suitable access device and into the patient's peritoneal cavity. The patient disconnects the catheter from the fresh dialysis solution bag and allows the solution to dwell within the cavity to transfer waste, toxins and excess water from the patient's bloodstream to the dialysis solution. After a dwell period, the patient drains the spent dialysis solution and then repeats the manual dialysis procedure. Tubing sets with “Y” connectors for the solution and drain bags are available that can reduce the number of connections the patient must make. The tubing sets can include pre-attached bags including, for example, an empty bag and a bag filled with dialysis solution.[0169]
• In CAPD, the patient performs several drain, fill, and dwell cycles during the day, for example, about four times per day. Each treatment cycle, which includes a drain, fill and dwell, takes about four hours.[0170]
• Automated peritoneal dialysis is similar to continuous ambulatory peritoneal dialysis in that the dialysis treatment includes a drain, fill, and dwell cycle. However, a dialysis machine automatically performs three or more cycles of peritoneal dialysis treatment, typically overnight while the patient sleeps.[0171]
• With automated peritoneal dialysis, an automated dialysis machine fluidly connects to an implanted catheter. The automated dialysis machine also fluidly connects to a source or bag of fresh dialysis solution and to a fluid drain. The dialysis machine pumps spent dialysis solution from the peritoneal cavity, through the catheter, to the drain. The dialysis machine then pumps fresh dialysis solution from the source, through the catheter, and into the patient's peritoneal cavity. The automated machine allows the dialysis solution to dwell within the cavity so that the transfer of waste, toxins and excess water from the patient's bloodstream to the dialysis solution can take place. A computer controls the automated dialysis machine so that the dialysis treatment occurs automatically when the patient is connected to the dialysis machine, for example, when the patient sleeps. That is, the dialysis system automatically and sequentially pumps fluid into the peritoneal cavity, allows for dwell, pumps fluid out of the peritoneal cavity, and repeats the procedure.[0172]
• Several drain, fill, and dwell cycles will occur during the treatment. Also, a final volume “last fill” is typically used at the end of the automated dialysis treatment, which remains in the peritoneal cavity of the patient when the patient disconnects from the dialysis machine for the day. Automated peritoneal dialysis frees the patient from having to manually perform the drain, dwell, and fill steps during the day.[0173]
• In general, the dialysis solution includes an osmotic agent, such as dextrose or other suitable constituent in any suitable amount, such as from about 1.5% to about 4.25% by weight. The dialysis solution further includes one or more electrolytes, such as sodium, calcium, potassium, magnesium chloride and/or the like in any suitable amount. The dialysis solution may also include other constituents, such as buffers including lactate and bicarbonate, or the like, and other constituents, such as stabilizers. The dialysis solution can be made from multiple solution components that can vary in the amounts and types of constituents thereof and have varying pH levels.[0174]
• A variety of different and suitable types of multi-part dialysis solutions can be utilized. For example, a multi-part bicarbonate-based solution can be found in U.S. patent application Ser. No. 09/955,248, entitled BIOCHEMICALLY BALANCED PERITONEAL DIALYSIS SOLUTIONS, filed on Sep. 17, 2001, the disclosure of which is incorporated herein by reference. An example of a multi-part lactate-based solution can be found in U.S. patent application Ser. No. 10/628,065, entitled DIALYSIS SOLUTIONS WITH REDUCED LEVELS OF GLUCOSE DEGRADATION PRODUCTS, filed on Jul. 25, 2003 the disclosure of which is herein incorporated by reference.[0175]
• Another example of a bicarbonate-based solution can be found in U.S. patent application Ser. No. 10/044,234, entitled BICARBONATE-BASED SOLUTIONS FOR DIALYSIS THERAPIES, filed on Jan. 11, 2002 and as further disclosed in U.S. Pat. No. 6,309,673, the disclosures of which are herein incorporated by reference. The bicarbonate-based solution can be made from solution components that have varying pH conditions, such as under moderate and extreme pH conditions. In an embodiment, the solution components can vary in pH from between about 1.0 to about 10.0. Once mixed, the desired pH of the mixed solution is a physiological acceptable level, such as between about 6.5 to about 7.6 (i.e., close to the pH of blood).[0176]
• For example, under moderate pH conditions, the bicarbonate-based solution can be formulated by the mixing of a bicarbonate concentrate with a pH that ranges from about 7.2 to about 7.9, preferably from about 7.4 to about 7.6, and an electrolyte concentrate with a pH that ranges from about 3.0 to about 5.0. Under extreme pH conditions, for example, the bicarbonate concentrate has a pH that can range from about 8.6 to about 9.5 and is mixed with an electrolyte concentrate that has a pH from about 1.7 to about 2.2. A variety of different and suitable acidic and/or basic agents can be utilized to adjust the pH of the bicarbonate and/or electrolyte concentrates. For example, a variety of inorganic acids and bases can be utilized, such as hydrochloric acid, sulfiric acid, nitric acid, hydrogen bromide, hydrogen iodide, sodium hydroxide, the like or combinations thereof.[0177]
• The solution components, such as the electrolyte concentrate and the dextrose concentrate, can then be mixed in the solution bag and then administered as a mixed solution to the patient during peritoneal dialysis. An illustrated example of a multi-chamber container that separately contains solution components of a dialysis solution according to embodiment of the present invention is shown in FIG. 9.[0178]
• It should be appreciated that the components of the dialysis solutions of the present invention can be housed or contained in any suitable manner such that the dialysis solutions can be effectively prepared and administered. In an embodiment, the present invention includes a multi-part dialysis solution in which two or more parts are formulated and stored separately, and then mixed just prior to use. A variety of containers can be used to house the various parts of the dialysis solution, such as separate containers (i.e., flasks or bags) that are connected by a suitable fluid communication mechanism.[0179]
• In an embodiment, a multi-chamber container or bag can be used to house the separate components of the solution including, for example, a dextrose concentrate and a buffer concentrate. In an embodiment, the separate components are mixed within the multi-chamber bag prior to use, such as applied during peritoneal dialysis.[0180]
• FIG. 9 illustrates a suitable container for storing, formulating, mixing and administering a dialysis solution, such as during continuous ambulatory peritoneal dialysis, according to an embodiment of the present invention. The[0181]multi-chamber bag380 has afirst chamber382 and asecond chamber384. The interior of the container is divided by aheat seal386 into the two chambers. It should be appreciated that the container can be divided into separate chambers by any suitable seal.
• In an embodiment, the container can be divided into separate chambers, such as two or more chambers, by a peel seal. With the use of a peel seal, a frangible connector or other suitable type of connector would not be required to mix the solution components within the multi-chamber bag. An example of a multi-chamber solution bag that includes a peel seal is disclosed in U.S. Pat. No. 6,319,243, the disclosure of which is herein incorporated by reference. As shown in FIG. 10, a[0182]container388 includes at least threechambers390,392 and394. Thechambers390,392 and394 are designed for the separate storage of liquids and/or solutions, that can be mixed within the container to form a mixed solution ready-for-use. It should be appreciated that more or less than three chambers can be utilized.
• The peelable seals[0183]396 and398 are provided between thechambers390,392 and394, respectively. Examples of peelable seals can be found in U.S. patent application Ser. No. 08/033,233 filed on Mar. 16, 1993 entitled “PEELABLE SEAL AND CONTAINER HAVING SAME”, the disclosure of which is herein incorporated by reference. The peelable seals allow for the selective opening of the chambers to allow for the selective mixing of the liquids contained therein.
• The[0184]container388 can also include tubular ports, such astubular ports400,402 and404 as shown in FIG. 10. The tubular ports are mounted to the container so as to allow fluid communication with the container and specifically withchambers390,392 and394. To this end, thetubular ports400,402 and404 can include a membrane that is pierced, for example, by a cannula or a spike or an administration set for delivery of the contents of the container to the patient. It should be appreciated that more or less than three ports can be utilized.
• As shown in FIG. 9, the[0185]multi-chamber container380 has afrangible connector406 to sealingly couple thefirst chamber382 to thesecond chamber384 instead of a peelable seal. To mix the solution within themulti-chamber bag380, thefrangible connector406 is broken.
• The first container or[0186]chamber382 includes twoport tubes408 of suitable sizes and lengths. It should be appreciated that more or less than two port tubes may be used. One of the port tubes, for example, can be utilized to add other constituents to thefirst chamber382 during formulation of the solution of the present invention, if necessary. The remaining port tube, for example, can be utilized to adaptedly couple thefirst chamber382 to the patient via a patient's administration line (not shown), be used to add additional other constituents or the like. The second container orchamber384 has asingle port tube410 extending there from. In an embodiment, theport tube410 is connected to a patient's administration line through which a solution can flow to the patient once the solution is mixed as described below.
• In an embodiment, the transfer of product within the[0187]multi-chamber bag380 can be initiated from thefirst chamber382 to thesecond chamber384 such that the components of each chamber can be properly mixed to form the dialysis solution of the present invention. In an embodiment, adextrose concentrate412 is contained in thefirst chamber382 and abuffer concentrate414 is contained in thesecond chamber384. It should be appreciated that any suitable type or number of solution components can be separated with a multi-chamber bag and then mixed to form a mixed solution prior to administration to the patient. Illustrative examples of peritoneal dialysis solutions include those described in U.S. patent application Ser. Nos. 09/955,298 and 10/628,065 and U.S. Pat. No. 6,309,673 as described above.
• The[0188]first chamber382 is smaller in volume than thesecond chamber384 such that the components of each chamber can be properly mixed once the transfer from the first chamber to the second chamber has occurred. Thus, themulti-chamber bag380 can house at least two solution component parts that after mixture will result in a ready-to-use dialysis solution. An example of the multi-chamber container is set forth in U.S. Pat. No. 5,431,496, the disclosure of which is incorporated herein by reference. The multi-chamber bag can be made from a gas permeable material, such as polypropylene, polyvinyl chloride or the like.
• It should be appreciated that the multi-chamber bag can be manufactured from a variety of different and suitable materials and configured in a number of suitable ways such that the dialysis solutions of the present invention can be effectively formulated and administered to the patient during medical therapy in any suitable manner. For example, the first chamber can be larger in volume than the second chamber and further adapted such that the dialysis solution of the present invention can be readily and effectively made and administered to the patient.[0189]
• In an embodiment, the dialysis solution is contained and administered from a multi-chamber solution bag during peritoneal dialysis, such as during CAPD. The solution bag can include multiple chambers that each contain separate components of the dialysis solution prior to mixing as discussed above. This may be necessary to maintain separation of the non-compatible solution components prior to mixing for purposes of stability, sterility, effectiveness or the like associated with the dialysis solution prior to use.[0190]
• In another embodiment, the solution components can be prepared and stored in separate containers and then mixed via an admix device prior to use, such as applied during automated peritoneal dialysis. As shown in FIG. 11, a first solution component, such as a dextrose concentrate[0191]416 and a second solution component, such as abuffer concentrate420 are stored in the respectiveseparate containers422 and424 or bags which are fluidly connected to anadmix device426 suitable for use during automated peritoneal dialysis, an example of which includes ADMIX HOMECHOICE by BAXTER INTERNATIONAL, INC. In addition to the first and second components, afirst bag428 andlast bag430 filled with a suitable solution can also be used during dialysis therapy as generally known.
• In an embodiment, an effective amount of the first solution component[0192]416 and thesecond solution component420 are drawn from each respective container and into aheater bag432 where the solution components (e.g., dextrose and buffer concentrates) can be mixed and heated prior to infuision into apatient434 during dialysis therapy. As further shown in FIG. 11, adrain line436 is coupled to theadmix device426 from which waste fluids can be removed from the patient during therapy.
• According to an embodiment of the present invention, the conductive polymer material can be used as a sensor to monitor solution compounding, such as during peritoneal dialysis. For example, the[0193]conductive polymer sensor438 can be attached to atube440 through which the mixed dialysis solution flows to the patient from themulti-chamber solution bag380 as shown in FIG. 9. Theconductive polymer sensor438 is in electric contact with acontroller442 or other like device such that a change in conductivity of the mixed dialysis solution that is fed to the patient can be monitored. Based on the conductivity level, one can monitor the pH level of the mixed solution to determine whether the solution components (e.g., dextrose concentrate and buffer concentrate) have been properly and sufficiently mixed to form the dialysis solution prior to use. If the dialysis solution is not properly mixed, the conductivity level will exist above or below a baseline conductivity level that is generally associated with a desired pH level of a dialysis solution that is ready-for-use. As previously discussed, the desired pH of the mixed dialysis solution is maintained at a physiological acceptable level, such as between about 6.5 to about 7.6 prior to use. Based on this information, adjustments can be made to the process such that the solution chemistry of the dialysis solution is modified for proper use. This can facilitate the safe and effective use of the solution during use, such as during dialysis therapy.
• As shown in FIG. 11, the[0194]conductive polymer sensor444 of the present invention can be applied during automated peritoneal dialysis. More specifically, theconductive polymer sensor444 of the present invention can be attached to thetube member446 through which a dialysis solution flows to the patient. The dialysis solution is a product of the mixing of solution components that are stored in separate solution bags as previously discussed. Theconductive polymer sensor444 can be attached to acontroller448 or other like device in electrical contact such that the conductivity level and thus the pH level of the solution that is administered to the patient can be monitored as previously discussed. Optionally, at least one additionalconductive polymer sensor450 in an embodiment can also be utilized as shown in FIG. 11. In this regard, the additional sensor(s) can be utilized to monitor the conductivity level of the solution components prior to mixing. This can be utilized to evaluate whether the solution components are maintained at desired pH levels based on a conductivity measurement as discussed above.
• It should be understood that various changes and modifications to the presently preferred embodiments described herein will be apparent to those skilled in the art. Such changes and modifications can be made without departing from the spirit and scope of the present invention and without diminishing its intended advantages. It is therefore intended that such changes and modifications be covered by the appended claims.[0195]

Claims (83)

The invention is claimed as follows:

1. A conductive material comprising a conductive polymer component electrically sensitive to a condition change when in contact with a solution used during dialysis therapy.

2. The conductive material ofclaim 1, wherein the conductive polymer component includes a polymer matrix and a conductive component that is incorporated in the polymer matrix.

3. The conductive material ofclaim 2, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

4. The conductive material ofclaim 2, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

5. The conductive material ofclaim 2, wherein the conductive component includes greater than about 10% by weight of the conductive material.

6. The conductive material ofclaim 2, wherein the conductive component is uniformly dispersed throughout the polymer matrix.

7. The conductive material ofclaim 2, wherein the conductive component includes a conductive fiber material that has an aspect ratio ranging from about 2:1 to about 30:1.

8. The conductive material ofclaim 1, wherein the conductive polymer component is selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

9. The conductive material ofclaim 1, wherein the condition change relates to a change in impedance due to patient access disconnection during dialysis.

10. The conductive material ofclaim 1, wherein the condition change relates to a change in conductivity based on a change in pH level of the solution administered during dialysis.

11. A coupler comprising a conductive polymer material that is so constructed and arranged to join tubing.

12. The coupler ofclaim 11, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophenes, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

13. The coupler ofclaim 11, wherein the conductive polymer material includes a polymer matrix and a conductive component incorporated within the polymer matrix, and wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

14. The coupler ofclaim 13, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

15. The coupler ofclaim 11, wherein the coupler has a generally cylindrical shape with a first opening and a second opening through which tubing can be joined.

16. The coupler ofclaim 15, wherein the coupler includes an extrudable product.

17. The coupler ofclaim 15, wherein the coupler includes a member that extends from at least a portion of an inner surface of the coupler allowing a length of a tubing joint that is formed with the coupler and tubing to be pre-set.

18. The coupler ofclaim 17, wherein the coupler includes an injection moldable product.

19. A sensor apparatus comprising an electrode including a conductive polymer material.

20. The sensor apparatus ofclaim 19, wherein the conductive polymer material includes a polymer matrix and a conductive component wherein the conductive component is incorporated in the polymer matrix.

21. The sensor apparatus ofclaim 20, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

22. The sensor apparatus ofclaim 21, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

23. The sensor apparatus ofclaim 19, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

24. The sensor apparatus ofclaim 19, wherein the electrode is attached to a tube member through which fluid flows.

25. The sensor apparatus ofclaim 19, wherein the tube member is selected from the group consisting of polyvinyl chloride, a non-polyvinyl chloride material and combinations thereof.

26. The sensor apparatus ofclaim 25, wherein the tube member and the electrode are attached via an attachment mechanism selected from the group consisting of solvent bonding, heating, laser welding, and radio frequency sealing.

27. The sensor apparatus ofclaim 19, wherein the electrode and at least a portion of the tube member attached to the electrode are secured to a device that has a hub design.

28. The sensor apparatus ofclaim 27, wherein the hub design includes a housing within which the electrode can be secured.

29. The sensor apparatus ofclaim 27, wherein the hub design includes a base member against which the electrode can be secured.

30. The sensor apparatus ofclaim 19 further comprising a controller in electrical contact with the electrode allowing detection of a condition change selected from the group consisting of detection of a change in impedance as the fluid flows through the tube member, detection of a change in conductivity based on a change in pH of the fluid as the fluid flows through the tube member, and combinations thereof.

31. The sensor apparatus ofclaim 19, wherein the electrode is formed into a dialyzer header.

32. An apparatus for detecting dislodgment of an access device inserted into a patient during medical therapy, the apparatus comprising:

a blood circuit connecting the patient to an extracorporeal blood system wherein the blood circuit includes a blood tubing set having a first tube member connected to a first access device and a second tube member connected to a second access device and wherein the first access device and the second access device are each insertable within the patient such that blood flows between the patient and the extracorporeal blood system via the blood circuit;

a first electrode and a second electrode in fluid contact with the blood and spaced apart from the first access device and the second access device, respectively, wherein at least one of the first electrode and the second electrode includes a conductive polymer material; and

a controller in electrical contact with each of the first electrode and the second electrode wherein the apparatus is capable of detecting a change in impedance in response to dislodgment of at least one of the first access device and the second access device.

33. The apparatus ofclaim 32, further comprising at least one additional electrode.

34. The apparatus ofclaim 32, wherein the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix.

35. The apparatus ofclaim 34, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

36. The apparatus ofclaim 34, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof, and mixtures thereof.

37. The apparatus ofclaim 32, wherein the medical therapy includes dialysis treatment selected from the group consisting of hemodialysis, hemodiafiltration, hemofiltration, continuous renal replacement therapy and home hemodialysis.

38. The apparatus ofclaim 32, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

39. An apparatus for monitoring delivery of a solution to a patient via an access device insertable within the patient during medical therapy, the apparatus comprising:

a tube member connecting the patient to a fluid system from which the solution flows into the patient via the access device;

an electrode connected to the tube member, wherein the electrode includes a conductive polymer material; and

a controller in electrical contact with the electrode allowing detection of a change in conductivity associated with the solution.

40. The apparatus ofclaim 39, wherein the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix.

41. The apparatus ofclaim 40, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

42. The apparatus ofclaim 40, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

43. The apparatus ofclaim 39, wherein the fluid system includes a plurality of solution components that are mixed to form the solution.

44. The apparatus ofclaim 43, wherein the detection of the change in conductivity is based on a change in pH associated with the solution.

45. The apparatus ofclaim 44, wherein the solution components have a varying pH level.

46. The apparatus ofclaim 45, wherein the solution components have a pH that ranges from about 1.8 to about 9.2.

47. The apparatus ofclaim 45, wherein the solution is monitored to determine whether the pH level of the solution is maintained at a physiological acceptable level after mixing of the solution components and prior to use as a dialysis solution.

48. The apparatus ofclaim 47, further comprising one or more additional electrodes for monitoring patient access conditions during dialysis therapy.

49. The apparatus ofclaim 43, wherein the solution components are mixed within a multiple-chamber solution bag to form a dialysis solution.

50. The apparatus ofclaim 43, wherein the solution components are separately contained in a respective solution bag prior to mixing to form a dialysis solution.

51. The apparatus ofclaim 39, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethlenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

52. A system for detecting dislodgment of an access device inserted into a patient during medical therapy, the system comprising:

a blood circuit connecting the patient to an extracorporeal blood system wherein the blood circuit includes a blood tubing set having a first tube member connected to a first access device and a second tube member connected to a second access device and wherein the first access device and the second access device are each insertable within the patient such that blood flows between the patient and the extracorporeal blood system via the blood circuit;

a first electrode and a second electrode in fluid contact with the blood and spaced apart from the first access device and the second access device, respectively, wherein at least one of the first electrode and the second electrode includes a conductive polymer material; and

a controller in electrical contact with each of the first electrode and the second electrode capable of detecting a change in impedance in response to dislodgment of at least one of the first access device and the second access device.

53. The system ofclaim 52 further comprising at least one additional electrode.

54. The system ofclaim 52 wherein the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix.

55. The system ofclaim 54, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and mixtures thereof.

56. The system ofclaim 54, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

57. The sensor apparatus ofclaim 52, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene)s and mixtures thereof.

58. The system ofclaim 57, wherein the medical therapy includes dialysis treatment selected from the group consisting of hemodialysis, hemodiafiltration, hemofiltration, continuous renal replacement therapy and home hemodialysis.

59. A system for monitoring delivery of a solution to a patient via an access device insertable within the patient during medical therapy, the system comprising:

a tube member connecting the patient to a fluid system from which the solution flows into the patient via the access device;

an electrode connected to the tube member, wherein the electrode includes a conductive polymer material; and

a controller in electrical contact with the electrode allowing detection of a change in conductivity associated with the solution.

60. The system ofclaim 59, wherein the conductive polymer material includes a polymer matrix and a conductive component that is incorporated in the polymer matrix.

61. The system ofclaim 60, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene, and mixtures thereof.

62. The system ofclaim 60, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

63. The system ofclaim 59, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

64. The system ofclaim 63, wherein the fluid system includes a plurality of solution components that are mixed to form the solution.

65. The system ofclaim 64, wherein the solution components have a varying pH level.

66. The system ofclaim 65, wherein a pH of the solution components can vary between about 1.8 to about 9.2.

67. The system ofclaim 65, wherein the change in conductivity is based on a change in a pH of the solution.

68. The system ofclaim 67, wherein the change in the pH is monitored to determine whether the pH of the solution is maintained at physiological acceptable level prior to use.

69. The system ofclaim 66, further comprising one or more additional electrodes for monitoring patient access conditions based on a change in impedance in response to dislodgment of the access device.

70. The system ofclaim 59, wherein the solution is selected from the group consisting of a dialysis solution, a peritoneal dialysis solution, a nutritional solution, a blood solution, an intravenous solution, and combinations thereof.

71. A method of detecting dislodgment of an access device during dialysis, the method comprising:

connecting a patient to a blood circuit having a pair of electrodes each coupled to a blood circuit in fluid contact with blood that flows through the blood circuit wherein at least one of the electrodes includes a conductive polymer material;

passing an electrical signal through the blood via the pair of electrodes thereby defining a loop along which an impedance can be measured; and

detecting a disconnection between the patient and the blood circuit in response to a change in the impedance.

72. The method ofclaim 71, wherein the conductive polymer material includes a polymer matrix and a conductive component incorporated within the polymer matrix.

73. The method ofclaim 72, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and combinations thereof.

74. The method ofclaim 71, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

75. The method ofclaim 71, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene)s and mixtures thereof.

76. A method of monitoring delivery of a solution to a patient during medical therapy, the method comprising:

connecting a patient to a tube member through which the solution can flow to the patient via an access device wherein the tube member has an electrode attached thereto, the electrode including a conductive polymer material;

passing an electrical signal into the solution via the electrode thereby allowing a conductivity associated with the solution to be measured; and

detecting a change in conductivity based on a change in pH of the solution.

77. The method ofclaim 76, wherein the conductive polymer material includes a polymer matrix and a conductive component incorporated within the polymer matrix.

78. The method ofclaim 77, wherein the polymer matrix is selected from the group consisting of polyvinyl chloride, acrylonitrile butadiene styrene, polycarbonate, acrylic, a cyclo olefin copolymer, a cyclo olefin copolymer blend, a metallocene-based polyethylene and combinations thereof.

79. The method ofclaim 77, wherein the conductive component is selected from the group consisting of stainless steel, fillers, carbon black, fibers thereof and mixtures thereof.

80. The method ofclaim 76, wherein the conductive polymer material includes a conductive polymer component selected from the group consisting of polyaniline, polypyrrole, polythiophene, polyethylenedioxythiophene, poly(p-phenylene vinylene) and mixtures thereof.

81. The method ofclaim 76, wherein the pH of the solution is monitored to determine whether the pH is maintained at a physiological acceptable level prior to use.

82. The method ofclaim 76, wherein the solution is derived from a mixture of solution components that have a pH ranging from about 1.8 to about 9.2.

83. The method ofclaim 76, further comprising one or more additional electrodes that are connected to the tube member such that a change in impedance based on dislodgement of the access device can be monitored.

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