while the present invention is susceptible of embodiment in various forms , as shown in the drawings , hereinafter will be described the presently preferred embodiments of the invention with the understanding that the present disclosure is to be considered as an exemplification of the invention , and it is not intended to limit the invention to the specific embodiments illustrated . with reference to fig1 - 15 , the hemodialysis system 1 of the present invention includes a reused dialysis machine 201 , a disposable cartridge 11 , an arterial blood line 3 including a needle 7 for connecting to a patient &# 39 ; s artery , and a venous blood line 5 including a needle 7 for connecting to a patient &# 39 ; s vein . with reference particularly to fig1 - 5 and 15 , the disposable cartridge 11 includes a housing 13 having conduits 17 providing a blood flow path 15 and conduits 21 providing a dialysis flow path 19 . preferably the cartridge &# 39 ; s blood flow path and dialysate flow path are conduits with an approximately 0 . 156 inch ( 3 - 5 millimeters ) inside diameter . the disposable cartridge 11 may be a single piece construction . however , preferably and as described herein , the disposable cartridge can be disassembled into multiple pieces such as to allow disengagement of a dialyzer 25 and filter 79 , but the multiple pieces can be assembled together to form a disposable cartridge 11 . preferably , the cartridge &# 39 ; s housing is made from federal drug administration approved materials . the presently preferred material for the cartridge &# 39 ; s housing is polycarbonate plastic . the disposable cartridge &# 39 ; s blood flow path 15 connects at one end to the arterial blood line 3 and at the other end to the venous blood line 5 . both the blood flow path 15 and dialysate flow path 19 travel through a dialyzer 25 to transport their respective fluids through closed loop systems wherein the dialysate flow path is isolated from the blood flow path by a semipermeable membrane ( not shown ). preferably , the dialysate flows in the opposite direction to blood flow within the dialyzer 25 which possesses an inlet 31 for receiving dialysate , an outlet 33 for expelling dialysate , an inlet 27 for receiving blood from a patient , and an outlet 29 for returning blood to a patient . more particularly , and as illustrated in fig1 , 3 and 9 , the disposable cartridge &# 39 ; s housing 13 includes a coupling 37 for connecting the dialyzer &# 39 ; s inlet 27 to the arterial blood line 3 , and a coupling 39 for connecting the dialyzer &# 39 ; s blood outlet 29 to the venous blood line 5 . in addition , the disposable cartridge &# 39 ; s housing 13 includes a cassette section 23 including conduits 21 for transporting dialysate back and forth from a reservoir 209 . to this end , the cassette 23 connects to the dialyzer &# 39 ; s inlet 31 and outlet 33 through couplings 47 and 43 . dialysate is received into the cassette 23 through the cassette &# 39 ; s coupling 47 . thereafter , the dialysate travels through dialysate flow path 19 ( within conduits 21 ) until entering the dialyzer 25 at the dialyzer &# 39 ; s inlet 31 . the dialysate then exits the dialyzer 25 at the dialyzer &# 39 ; s outlet 33 , and continues to travel through the dialysate flow path 19 through conduits 21 until exiting the cassette 23 at coupling 43 . preferably , the cartridge &# 39 ; s cassette 23 possesses two pump actuators 51 and 53 . a first pump actuator 51 is positioned upflow of the dialyzer 25 to pump dialysate through the dialysate flow path 19 to the dialyzer 25 . the second pump actuator 53 is positioned almost immediately downflow of the dialyzer 25 for pumping dialysate from the dialyzer 25 . by independently controlling the operation of the first pump actuator 51 relative to the second pump actuator 53 allows one to increase or decrease the pressure of the dialysate fluid within the dialyzer 25 . preferably the disposable cartridge &# 39 ; s housing 13 includes a third pump actuator 55 which is positioned within the housing &# 39 ; s coupling 37 which connects to the arterial blood line 3 . this third pump actuator 55 pumps blood through the blood flow path 15 , and is preferably positioned upflow of the dialyzer 25 . as best illustrated in fig2 , 7 and 8 , the disposable cartridge 11 includes a filter 79 . the filter 79 includes a housing 81 for encapsulating filter materials for removing toxins from the dialysate liquid . the filter material may be of a composition and construction known or as can be determined by those skilled in the art for removing the various wastes , primarily urea and creatine , from blood . the filter 71 includes an inlet 83 and an outlet 85 . the filter &# 39 ; s inlet 83 connects to the cassette &# 39 ; s coupling 43 , and the filter &# 39 ; s outlet 85 connects to a reservoir &# 39 ; s inlet 211 , described in greater detail below . in a preferred embodiment , the filter &# 39 ; s housing 81 includes a vapor membrane 87 illustrated in fig7 and 8 . the vapor membrane 87 is a semipermeable membrane capable of releasing gases including ammonia , but not liquids and particularly not the dialysate liquid , flowing through the filter 79 . as discussed in detail below , the disposable cartridge 11 possesses various sensors for monitoring the dialysis occurring within the dialyzer 25 . as illustrated in fig5 - 10 , the preferred disposable cartridge 11 includes two pairs of flow sensors 93 and pressure sensors 95 in the cassette for measuring the fluid flow and pressure of the dialysate in the dialysate flow path 19 . preferably , the cassette flow sensors 93 are positioned upflow and downflow , respectively , of the dialyzer 25 . in a preferred embodiment , each flow sensor 93 includes a circular chamber 91 in the dialysate flow path and rotatable spoked wheel ( not shown ) within the chamber 91 which is rotated by the flow of dialysate . preferably , the wheel spokes includes two magnets of opposite polarity which reveal the wheel &# 39 ; s rotational position and rotational velocity which is used to determine fluid flow . preferably , the cassette pressure sensors 95 for measuring dialysate pressure are also positioned upflow and downflow , respectively , of the dialyzer 25 for measuring the pressure of the dialysate prior to the dialysate entering the dialyzer 25 and subsequent to the dialysate leaving the dialyzer 25 . the cassette &# 39 ; s pressure and flow sensors may be federal drug administration approved sensors as can be selected by those skilled in the art . preferably , the disposable cartridge possesses still additional sensors 97 for measuring the pressure and fluid flow of the blood passing through the blood flow path 15 both immediately after the blood is received from a patient , and prior to returning the blood to a patient . in a preferred embodiment , both the pressure and fluid flow measurements of the blood are made by a single sensor . as best illustrated in fig5 , 9 , 10 , 13 and 15 , the preferred cartridge 11 includes a first pressure / fluid sensor 97 within coupling 37 for measuring the pressure and fluid flow of the blood as it is received by the arterial blood line 3 prior to the blood entering the dialyzer 25 . in addition , preferably the cartridge possesses a second pressure / fluid sensor 97 within the coupling 39 for measuring the pressure and fluid flow of the blood prior to the blood being returned to the patient through the venous blood line 5 . to transfer measurements produced by the cassette flow sensors and pressure sensors , the disposable cartridge 11 possesses electrical terminals 101 . the hemodialysis system &# 39 ; s dialysis machine 201 is best illustrated in fig1 - 5 . preferably , the dialysis machine 201 possesses a case 205 having a cavity 207 for encapsulating and protecting the various components of the dialysis machine 201 and disposable cartridge 11 . preferably , the case 205 is of a size suitable for travel in an overhead bin of a commercial airliner . the dialysis machine 201 possesses a reservoir 209 for storing the dialysate during the hemodialysis procedure . a preferred reservoir stores 1 gallon ( 3 . 785 liters ) of dialysate which can be introduced into the reservoir through the reservoir &# 39 ; s removable cap 215 . in addition , the reservoir 209 includes an inlet 211 and an outlet 213 . as best illustrated in fig7 , the reservoir &# 39 ; s inlet 211 connects to the disposable cartridge &# 39 ; s filter &# 39 ; s outlet 85 . meanwhile , the reservoir &# 39 ; s outlet 213 connects to the disposable cartridge &# 39 ; s connector 47 . preferably the dialysis machine possesses a heater 221 ( illustrated in fig1 ) which is thermally coupled to the reservoir 209 for heating and maintaining the temperature of the dialysate at a desired temperature . preferably the dialysis machine 201 includes a tray 219 for supporting and mating to the disposable cartridge &# 39 ; s housing 13 , dialyzer 25 , arterial line coupling 37 , and venous line coupling 39 . the tray 219 may include latches 225 for locking the disposable cartridge 11 in engagement with the dialysis machine 201 . in the preferred embodiment , the tray 219 also includes three pump motors ( 227 , 229 and 231 ) for coupling to the disposable cartridge &# 39 ; s three pump actuators ( 51 , 53 and 55 ). with reference to fig5 , 6 and 11 , the dialysis machine includes a first pump motor 227 for coupling with the disposable cartridge &# 39 ; s first pump actuator 51 , a second pump motor 221 for coupling with the disposable cartridge &# 39 ; s second pump actuator 53 , and a third pump motor 231 for coupling with the disposable cartridge &# 39 ; s third pump actuator 55 . preferably , the pump motors are traditional commercial off - the - shelf electric rotary motors as can be selected by those skilled in the art . as illustrated in fig6 , preferably each pump actuator ( 51 , 53 and 55 ) does not employ deformable members for providing pumping action , such as employed with a common roller pump engaging an arterial line or venous line . instead , the preferred pump actuators possess a sliding vane construction . to this end , each pump actuator includes an inlet 57 for introducing fluid into a cavity 63 and an outlet 59 for expelling such fluids . furthermore , each pump actuator includes a circular rotor 65 having slots 67 for receiving radially moving vanes 69 . centrifugal force , hydraulic pressure and / or a biasing means , such as springs or push rods , push the vanes to the walls of the cavity 63 to form chambers formed by the rotor , vanes and cavity sidewall . in the preferred embodiment illustrated in fig6 , centrifugal force caused by rotation of the rotor pushes the vanes to the cavity sidewall . preferably , the cavity 63 and rotor 67 are substantially circular and the rotor is positioned within the larger cavity . however , the rotor &# 39 ; s center and cavity &# 39 ; s center are axially offset ( eccentric ) from one another . in operation , the rotor 65 and vanes 69 form an impeller . as the rotor rotates , fluid enters the pump actuator through the inlet 57 . rotation of the rotor and vanes pump fluid to be propelled from the pump actuator &# 39 ; s outlet 59 . preferably , each pump actuator is made of substantially non - deformable materials including federal drug administration approved plastics . as used herein , the term “ non - deformable ” is not meant to mean that the pump actuator components will not undergo some insignificant deformation during pump operation . however , the non - deformable pump actuator components do not deform in a manner to provide pumping action such as provided by a peristaltic roller pump engaging a flexible tube , such as a blood line , as is commonly employed for current hemodialysis treatment . in the preferred embodiments , the pump actuator &# 39 ; s housing and rotor are made of polycarbonate , and the pump actuator &# 39 ; s vanes are made of polyether ether ketone ( peek ). still with reference to fig6 , the pump actuator &# 39 ; s rotor 63 may be connected to the electric motor 67 by various constructions known to those skilled in the art . for example , the rotor may include a shaft which is keyed to form a press fit with a corresponding receptacle formed in the rotor . however , in the preferred embodiment illustrated in fig6 , the motor 227 and rotor 65 are coupled utilizing magnets 71 . as illustrated , a preferred rotor possesses six magnets wherein the polarity ( north - south direction ) is alternated for each adjacent magnet 71 . similarly , the motor 227 contains six additional magnets 71 wherein the polarity of each magnet is alternated . when a disposable cartridge 11 is coupled to the dialysis machine 201 , the motor magnets are positioned and aligned to come in close contact with the rotor magnets . magnetic forces couple the pump motors to the pump actuators so that controlled activation of the pump motors rotates the rotors , and thus operates the pump actuators . as discussed in detail below , in addition to the sensors found in the disposable cartridge 11 , the preferred dialysis machine 201 also possesses various sensors for monitoring proper operation of the hemodialysis system 1 . for example , the dialysis machine preferably includes a temperature sensor 223 for measuring the temperature of the dialysate within the reservoir 209 . in addition , the dialysis system includes an ammonia sensor 237 ( see fig1 ) which is positioned adjacent to the filter &# 39 ; s vapor membrane 87 for detecting any ammonia within the filter 79 . as illustrated in fig2 , 3 and 12 , preferably the dialysis machine 201 also includes a pair of sensors ( 239 and 241 ) and a valve 245 connected to the venous blood line 5 for providing still additional redundant safety to a patient . the additional sensors include a pressure sensor 239 for measuring the pressure of the blood in the venous blood line 5 and a bubble sensor 241 to determine whether there are any unwanted air bubbles in the venous blood line 5 . in the event that the blood pressure is not within a predetermined range or in the event that an unwanted air bubble is detected , a pinch valve 245 is made to close . with reference to fig1 , the dialysis machine 201 includes a processor 249 , a user interface 25 , and a power supply 253 for providing power to the processor 249 , user interface 251 , pump motors , and sensors . the processor 249 is connected to the dialysis machine sensors ( including reservoir level sensor 217 , blood leak sensor 235 , ammonia sensor 237 , venous blood line pressure sensor 239 , and venous blood line bubble sensor 241 ), three pump motors 227 , 229 and 231 , and pinch valve 245 by traditional electrical circuitry . in addition , the dialysis machine possesses electrical terminals 247 ( see fig1 ) for connecting to the disposable cartridge &# 39 ; s electrical terminals 101 so as to connect the processor 249 with the disposable cartridge &# 39 ; s sensors ( including flow and pressure sensors ). the processor may be a general purpose computer or microprocessor including hardware and software as can be determined by those skilled in the art to monitor the various sensors and provide automated or directed control of the heater , pumps , and pinch valve . the processor may be located within the electronics of a circuit board or within the aggregate processing of multiple circuit boards . in operation , the processor 249 is electrically connected to the first , second and third pump motors for controlling the activation and rotational velocity of the pump motors , which in turn controls the pump actuators , which in turn controls the pressure and fluid velocity of blood through the blood flow path and dialysate through the dialysate flow path . by independently controlling operation of the first and second pump actuators , the processor can maintain , increase or decrease the pressure and / or fluid flow within the dialysate flow path within the dialyzer . moreover , by controlling all three pump actuators independently , the processor 249 can control the pressure differential across the dialyzer &# 39 ; s semipermeable membrane to maintain a predetermined pressure differential ( zero , positive or negative ), or maintain a predetermined pressure range . for example , most hemodialysis is performed with a zero or near zero pressure differential across the semipermeable membrane , and to this end , the processor can monitor and control the pumps to maintain this desired zero or near zero pressure differential . alternatively , the processor may monitor the pressure sensors and control the pump motors , and in turn pump actuators , to increase and maintain positive pressure in the blood flow path within the dialyzer relative to the pressure of the dialysate flow path within the dialyzer . advantageously , this pressure differential can be affected by the processor to provide ultrafiltration and the transfer of free water and dissolved solutes from the blood to the dialysate . moreover , the processor monitors all of the various sensors to ensure that the hemodialysis machine is operating efficiently and safely , and in the event that an unsafe or non - specified condition is detected , the processor corrects the deficiency or ceases further hemodialysis treatment . for example , if the venous blood line pressure sensor 239 indicates an unsafe pressure or the bubble sensor 241 detects a gaseous bubble in the venous blood line , the processor signals an alarm , the pumps are deactivated , and the pinch valve 245 is closed to prevent further blood flow back to the patient . similarly , if the blood leak sensor 235 detects that blood has permeated the dialyzer &# 39 ; s semipermeable membrane , the processor 249 signals an alarm and ceases further hemodialysis treatment . the dialysis machine &# 39 ; s user interface 251 may include a keyboard or touch screen for enabling a patient or medical personnel to input commands concerning treatment or enable a patient or medical personnel to monitor performance of the hemodialysis system . moreover , the processor may include wi - fi connectivity for the transfer of information or control to a remote location . as mentioned above , the hemodialysis system 1 incorporates numerous improved sensors never before incorporated into a hemodialysis device . the improved sensors include ammonia sensor 237 , fluid level sensor 217 , and blood leak sensor 235 . each of these sensors is described in greater detail below . as also mentioned above , the at least one ammonia sensor 237 is positioned adjacent to the filter &# 39 ; s vapor membrane 87 and configured for detecting any ammonia within the filter 79 . in a bit more detail , in at least one embodiment , each ammonia sensor 237 incorporates a heater ( not shown ) having the following parameters : in at least one embodiment , due to the nature of the chemo - sensitive film on the ammonia sensor 237 , it is important that the temperature rise from the heater be repeatable and consistent over the lifetime of the ammonia sensor 237 . to that end , it is also important to control the power applied to the heater as consistently as possible , especially knowing the resistance of the heater changes over the lifetime of the ammonia sensor 237 . in at least one embodiment , the ammonia sensor 237 uses a single load resistor in series with the heater . this configuration is extremely sensitive to variations in vcc as well as r h . using nominal vcc = 3 . 3v ± 3 . 0 % and r l = 36 . 5ω ± 1 . 0 % produces p h = 0 . 0669 w ± 10 . 3 % ( with design center p h = 0 . 0667 w ) as demonstrated in the following table : in at least one embodiment , in order to more tightly control the power dissipation in the heater , the circuit shown in fig1 is used . the ldo is used to force a constant current through r l , and r p is used to balance the current through r h . using v fb = 0 . 8v ± 1 . 25 %, r l = 13 . 0ω ± 1 %, r p = 69 . 8ω ± 1 %, p h = 0 . 0658 w ± 1 . 65 % ( with design center p h = 0 . 0661 w ) as demonstrated in the following table : the maximum power dissipation is p ( r l )= 0 . 050 w and p ( rp )= 0 . 076 w , which are well within normal operating parameters of 1 / 10 w , 0603 resistors . the maximum vout required by the ldo is 3 . 12 v ( v ( r h )+ v fb ). the dropout voltage at 62 ma is ˜ 80 mv . v cc ( min )= 3 . 12 + 0 . 08 = 3 . 20 v , which requires a vcc supply of 3 . 3v ± 3 %. in at least one embodiment , the sensitive layer of the ammonia sensor 237 has chemo resistive characteristics . due to the fabrication of the sensitive layer , the reference resistance , r 0 ( ambient conditions , synthetic air ), is unable to be tightly controlled . gas sensing is performed by taking the current sensing resistance , r s , and dividing it by the ambient resistance , as the sno 2 gas sensing layer reduces the nh 3 ( as well as other gasses ) at high temperatures , under bias and conductivity increases . the r s / r 0 ratio is indicative of the gas concentration , and is used for calibration and threshold detection . the sensitive layer characteristics are shown in the table below : r 0 / r s ratio ( 1 ppm nh 3 ) since the output of the ammonia sensor 237 will be read across r l ( differential ), v ( r l ) must be kept below differential full scale input range of the converter ( 0 . 5v ) for proper in - limits conversion . due to the wide dynamic range of r 0 , it is apparent that multiple resistances need to be switched in order to manage the readout of the ammonia sensor 237 . the following illustrates the configuration of at least one embodiment . with the low currents involved , the gpio signals can be assumed to be gnd ( or repeatably close to gnd ). the gpio pin is either left in the high - z condition ( floating ), or driven 0 . this configuration is used to ensure the highest voltage practical across the sensitive layer in order to ensure proper reduction at the sensitive layer gain boundaries . the maximum current and power through the sensitive layer is defined by the following formula : it should also be noted that the internal gain of the converter can be used to increase the dynamic range once the baseline r 0 is determined after warm - up . as also mentioned above , the blood leak sensor 235 is positioned and configured for detecting whether blood has permeated the semipermeable membrane of the dialyzer 25 . in a bit more detail , in at least one embodiment , the blood leak sensor 235 uses the principle of optical absorption to determine the presence of blood in the dialysate . using two separate wavelength emitters , the blood leak sensor 235 compensates for changes in the dialysate clarity . as also mentioned above , the at least one level sensor 217 is positioned and configured for monitoring and measuring the level of the dialysate fluid in the dialysate reservoir 209 ( fig1 and 15 ). in at least one embodiment , the fluid is contained within the reservoir 209 , and the level sensor 217 is positioned outside and adjacent the reservoir 209 . the level sensor 217 provides a safety critical function as it monitors the dialysate reservoir 209 for increases and decreases in fluid level . aside from catastrophic fluid loss ( i . e ., ruptured reservoir 209 or flow path 19 ), gain or loss of dialysate fluid indicates the pressure balance across the dialyzer 25 is incorrect and must be adjusted . in a bit more detail , in at least one embodiment , the level sensor 217 uses change in capacitance to determine the fluid level in the reservoir 209 . a series of electrodes 260 and a ground surface 262 are positioned adjacent to the reservoir 209 , and the change in capacitance at a given electrode 260 reflects the presence or absence of the mildly conductive dialysate fluid . in at least one embodiment , as illustrated in fig1 , the electrodes 260 are arranged in a staggered pattern , providing overlap between electrodes 260 . this overlap also allows for relatively better level resolution than non - overlapped electrodes 260 . the capacitive coupling between the electrodes 260 and ground surface 262 (“ gnd ”) changes depending on the presence of the dialysate fluid . this change in capacitance is measured and used to determine the fluid level across all electrodes 260 . among the electrodes 260 , the level sensor 217 includes a wet reference electrode 264 and a dry reference electrode 266 , which are used as references for the capacitive coupling of the dialysate fluid , and the ambient capacitive coupling . in at least one embodiment , the wet reference electrode 264 is positioned for always being below the dialysate fluid level , and the dry reference electrode 266 is positioned for always being above the dialysate fluid level during normal operation . with continued reference to fig1 , in at least one embodiment , the level sensor 217 further provides a capacitance - to - digital converter ( not shown ), which measures the capacitance between each of the electrodes 260 and ground surface 262 . the level sensor 217 also provides an ac shield output 268 , which is in - phase with the driven electrode 260 , and is used to isolate the electrode 260 from stray ground coupling . the ac shield 268 is used in a plane behind the electrodes 260 to shield the electrodes 260 from stray ground , and in an electrode position to assure equal loading for each of the electrodes 260 . in at least one embodiment , each electrode 260 is a symmetric square rotated ninety degrees , with an overall height of 12 mm and an overall width of 12 mm ( a rotated square with all sides of 8 . 49 mm long ) with an area of 72 mm 2 . the electrodes 260 are spaced vertically at 7 . 5 mm between electrode 260 centers . the volume of dialysate fluid represented by this space is proportional to the cross - section area at the fluid level . in the exemplary embodiment , the cross - sectional area of the reservoir 209 is 3 . 102 mm 2 . the volume represented by a deviation in level is calculated using the following equation : in the exemplary embodiment , the level sensor 217 has a basic span (± 18 . 75 mm ) of ± 58 ml , which represents 5 . 8 % of the dialysate fluid . in closing , regarding the exemplary embodiments of the present invention as shown and described herein , it will be appreciated that a portable hemodialysis machine and disposable cartridge is disclosed . because the principles of the invention may be practiced in a number of configurations beyond those shown and described , it is to be understood that the invention is not in any way limited by the exemplary embodiments , but is generally directed to a portable hemodialysis machine and disposable cartridge and is able to take numerous forms to do so without departing from the spirit and scope of the invention . it will also be appreciated by those skilled in the art that the present invention is not limited to the particular geometries and materials of construction disclosed , but may instead entail other functionally comparable structures or materials , now known or later developed , without departing from the spirit and scope of the invention . furthermore , the various features of each of the above - described embodiments may be combined in any logical manner and are intended to be included within the scope of the present invention . groupings of alternative embodiments , elements , or steps of the present invention are not to be construed as limitations . each group member may be referred to and claimed individually or in any combination with other group members disclosed herein . it is anticipated that one or more members of a group may be included in , or deleted from , a group for reasons of convenience and / or patentability . when any such inclusion or deletion occurs , the specification is deemed to contain the group as modified . unless otherwise indicated , all numbers expressing a characteristic , item , quantity , parameter , property , term , and so forth used in the present specification and claims are to be understood as being modified in all instances by the term “ about .” as used herein , the term “ about ” means that the characteristic , item , quantity , parameter , property , or term so qualified encompasses a range of plus or minus ten percent above and below the value of the stated characteristic , item , quantity , parameter , property , or term . accordingly , unless indicated to the contrary , the numerical parameters set forth in the specification and attached claims are approximations that may vary . at the very least , and not as an attempt to limit the application of the doctrine of equivalents to the scope of the claims , each numerical indication should at least be construed in light of the number of reported significant digits and by applying ordinary rounding techniques . notwithstanding that the numerical ranges and values setting forth the broad scope of the invention are approximations , the numerical ranges and values set forth in the specific examples are reported as precisely as possible . any numerical range or value , however , inherently contains certain errors necessarily resulting from the standard deviation found in their respective testing measurements . recitation of numerical ranges of values herein is merely intended to serve as a shorthand method of referring individually to each separate numerical value falling within the range . unless otherwise indicated herein , each individual value of a numerical range is incorporated into the present specification as if it were individually recited herein . the terms “ a ,” “ an ,” “ the ” and similar referents used in the context of describing the present invention ( especially in the context of the following claims ) are to be construed to cover both the singular and the plural , unless otherwise indicated herein or clearly contradicted by context . all methods described herein can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context . the use of any and all examples , or exemplary language ( e . g ., “ such as ”) provided herein is intended merely to better illuminate the present invention and does not pose a limitation on the scope of the invention otherwise claimed . no language in the present specification should be construed as indicating any non - claimed element essential to the practice of the invention . specific embodiments disclosed herein may be further limited in the claims using consisting of or consisting essentially of language . when used in the claims , whether as filed or added per amendment , the transition term “ consisting of ” excludes any element , step , or ingredient not specified in the claims . the transition term “ consisting essentially of ” limits the scope of a claim to the specified materials or steps and those that do not materially affect the basic and novel characteristic ( s ). embodiments of the present invention so claimed are inherently or expressly described and enabled herein . it should be understood that the logic code , programs , modules , processes , methods , and the order in which the respective elements of each method are performed are purely exemplary . depending on the implementation , they may be performed in any order or in parallel , unless indicated otherwise in the present disclosure . further , the logic code is not related , or limited to any particular programming language , and may comprise one or more modules that execute on one or more processors in a distributed , non - distributed , or multiprocessing environment . while several particular forms of the invention have been illustrated and described , it will be apparent that various modifications can be made without departing from the spirit and scope of the invention . therefore , it is not intended that the invention be limited except by the following claims .
a portable hemodialysis system is provided suitable for in home use . the hemodialysis system includes a disposable cartridge and a reused dialysis machine . the disposable cartridge includes a dialyzer , and a dialysate flow path and a blood flow path which flow in opposing directions through the dialyzer . in addition , the disposable cartridge possesses pump actuators for pumping dialysate and blood through their respective flow paths . the pump actuators having non - deformable components including a housing having a central cavity forming an internal sidewall , a rotor eccentrically positioned within the cavity having radially aligned slots at the rotor &# 39 ; s periphery , and vanes slideably positioned in the slots to slide in and out of the slots so as to seal with the cavity &# 39 ; s internal sidewall creating vane chambers that pump blood or dialysate .