turning to fig4 , a cycler 30 includes a dialysate container 11 connected to a pump 31 . the pump 31 is connected to a pressure sensor 32 . the pump 31 and pressure sensor 32 are disposed in - line in a lumen 33 that connects the dialysate container 11 to a catheter 34 . control valves are provided at 35 , 36 . a drain container 13 is also connected to a pump 36 which is connected to a sensor 37 . the pump 36 and sensor 37 are also connected in - line to a lumen 38 which connects the drain container 13 to the catheter 34 . control valves are again provided at 41 , 42 . during the fill , the pump 31 pumps dialysate from the container 11 through the lumen 33 and catheter 34 into the peritoneum ( not shown ) of the patient 12 . during this time , the sensor 37 monitors and measures the intraperitoneal pressure . a signal is sent to the controller of the cycler 30 shown schematically at 43 . a control panel is indicated generally at 44 . during the drain , the sensor 31 can accurately monitor and measure the intraperitoneal pressure of the patient 12 . in the embodiment illustrated in fig4 , no pumps or control valves are disposed between the sensor 32 and the patient 12 . turning to fig5 , a cycler 50 is illustrated which includes reversible pumping chambers 51 , 52 with sensors 53 , 54 disposed between the reversible pumping chambers 51 , 52 and the patient 12 respectively . control valves 55 and 56 are disposed on another side of the reversible pumping chamber 51 and the sensor 53 and control valves 57 , 58 are provided on either side of the reversible pumping chamber 52 and sensor 54 . the sensors 53 , 54 actually measure the pressure on the diaphragms of the reversible pumping chambers 51 , 52 . turning to fig6 , a cycler 60 is illustrated with a chamber 61 for accommodating the drain container 13 and a chamber 62 for accommodating the dialysate container 11 . each chamber 61 , 62 is equipped with an integrated valve assembly and pressure sensor shown at 63 , 64 . in the embodiment 60 shown in fig6 , the chamber 61 must be capable of being evacuated . dialysate may flow from the dialysate container 11 by way of gravity or pressure fill . again , the sensors of the valve assembly / sensor combinations 63 , 64 monitor the intraperitoneal pressure of the patient 12 as discussed above . in the embodiment 70 illustrated in fig7 , the dialysate container 11 and drain container 13 are both connected to integrated control valves and pressure sensors 71 , 72 . each of the integrated control valves and pressure sensors 71 , 72 are connected to lumens 73 , 74 respectively which are connected to the catheter 75 a by way of a y - connection . the details of all the y - connections and clamps are not shown but are known to those skilled in the art . flow from the dialysate container 11 to the patient is carried out under the gravitational head shown at 75 while flow from the patient to the drain container 13 is carried out under the gravitational head shown at 76 . fig8 illustrates one in - line pressure sensor 80 that is suitable for use with the present invention . redundant load cells 81 , 82 are connected to the flexible pressure sensing membrane 83 by a vacuum connected by the line 84 , 85 . a lumen connecting the cycler to the patient is shown at 86 . fig9 illustrates a dual - pumping chamber cassette 87 which includes an output line 88 which connects the cassette 87 to the patient and an input line 89 connecting the patient to the cassette 87 . the line 90 connects the cassette 87 to the dialysate container ( not shown ). each pumping chamber 91 , 92 is in communication with all three lines 88 , 89 and 90 . thus , every line can be connected to either pumping chamber 91 , 92 . the pumping chambers 91 , 92 are bound on one side by a common diaphragm shown at 93 . flow is controlled by the use of diaphragm valves shown at 94 , 95 , 96 and 97 . pressure sensors are shown at 120 , 121 , 122 , 123 , 124 and 125 . however , pressure sensors 123 and 120 are the sensors used to measure intraperitoneal pressure in accordance with the present invention . the remaining sensors 121 , 122 , 124 , 125 are used to monitor the operation of the pumps 126 , 127 . when the left diaphragm pump 126 is pushing dialysate to the patient , the sensor 123 can measure the intraperitoneal pressure through the line 89 . when the left diaphragm pump 126 is draining fluid from the patient through the line 89 , the sensor 120 can measure intraperitoneal pressure through the line 88 and while the right pump 127 is pumping fluid to the drain container ( not shown ) through the drain line shown schematically at 128 . when the right diaphragm pump 127 is being used to drain fluid from the patient , the sensor 120 can measure intraperitoneal pressure while the left diaphragm pump 126 is pumping fluid to the drain container ( not shown ) through the drain line shown schematically at 129 . fig1 and 11 illustrate a dual - lumen catheter 100 which includes separate passageways 101 , 102 . the employment of a dual lumen catheter 100 as compared to a dual lumen patient line can move the point at which the pressure is measured to within the peritoneum itself by way of communication through the separate flowpaths 101 , 102 . the dual lumen catheter 100 installs like a single lumen catheter , yet will function either as a flow through or a standard catheter . both fluid pathways 101 , 102 are used to withdraw and deliver fluid during the drain and fill . while one pathway delivers fluid , the other pathway drains . the end section , shown generally at 103 , is perforated . a comparison of an apd therapy for a prior art apd cyclers and one manufactured in accordance with the present invention are summarized as follows : inspection of table 1 shows that cycler 1 woke the patient at around 4 : 30 in the morning with a negative uf alarm at the beginning of fill 5 . the patient bypassed the alarm because he did not feel overfull and immediately fell back asleep . he woke up about minutes later when he had difficulty breathing and felt extremely overfull . he manually drained about 1500 ml but was unable to go back to sleep . he filed a formal product complaint with the manufacturer . the data of table i shows that cycler 2 ran a completely normal therapy but the total therapy clearance ( calculated based upon the sum of the night patient volumes ) was only 84 . 5 % of that obtained by cycler 3 , which was using the cycler that used the method of the current invention . the data of table 1 shows that cycler 3 ran a completely normal therapy and that the fill volume was limited on one occasion by the maximum fill volume but on four occasions by the patient &# 39 ; s intraperitoneal pressure . this patient never felt any discomfort and had no alarms during the night . the limit on the ipp prevented him from being overfilled even though he had successive drains that were not complete . the volume of fluid in his peritoneum never exceeded 3 liters . the patient on cycler 1 had an intraperitoneal pressure in excess of 14 mm hg during dwells 3 and 4 . his breathing may have been impaired and his heart may have had to work harder but the discomfort was not enough to wake him up from a sound sleep until it peaked at 4 , 099 ml during dwell 5 . in conclusion , the method of the present invention provides for optimum fills and therefore more clearance while preventing overfills that bring discomfort and inhibit the function of vital body organs . a negative uf alarm would seldom occur because overfills of the required magnitude would be prevented by the ipp sensors . in order to calculate the ipp , one may first calculate the patient head height correction using conservation of energy : the velocity v of fluid through the patient line is the same at both ends of the line as is the fluid density , so this equation can be written as ( p 2 − p 1 )− pa g ( h 2 h )+ frictional losses = 0 frictional losses = 39130 ( gram / cm )/( cm 2 - sec 2 ) with flow of 197 cm / min in a 4 mm id line at a velocity of approximately 172 cm / sec , wherein frictional losses = 39130 ( gram / cm )/( cm 2 - sec 2 ) with flow of 197 cmn / min in a 4 mm id line at a velocity of approximately 172 cm / sec , wherein the patient head height can be established at the beginning of each fill . any changes in the head height that occur during the fill can be attributed to an increase in intraperitoneal pressure ( ipp ) since the patient is asleep . turning to fig1 , the concentration gradient between the urea concentration 110 in the patient &# 39 ; s blood and the urea concentration 111 in the dialysate for typical apd cyclers is illustrated graphically . comparing the results illustrated in fig1 and 14 , it is evident that apd cyclers equipped with the sensors of the present invention provide superior results . specifically , the data illustrated graphically in fig1 was obtained using a prior art apd cycler . the data obtained in fig1 was obtained using an apd cycler utilizing two sensors for monitoring intraperitoneal pressure . note that the urea concentration 110 in the bloodstream is lower in fig1 than in fig1 . further note , the dialysate volume or fill volume is lower for the therapy illustrated in fig1 than the therapy illustrated in fig1 . thus , the present invention provides improved urea clearance with lower fill volumes . 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 may be made without departing from the spirit and scope of the present invention and without diminishing its attendant advantages . it is , therefore , intended that such changes and modifications be covered by the appended claims .
a method of performing peritoneal dialysis is provided . the method involves sensing a pressure in a fluid upstream or downstream of a pump chamber and adjusting a planned peritoneal dialysis treatment based on the sensed pressure to avoid an alarm condition . an intra - peritoneal pressure may be sensed and may be related to a head height of a peritoneal dialysis patient relative to a pump actuation . the fill volume to the peritoneal dialysis patient may also be limited due to the sensed pressure .