various embodiments are described more fully below with reference to the accompanying drawings , which form a part hereof , and which show specific example embodiments for practicing various embodiments . however , other embodiments may be implemented in many different forms and should not be construed as limited to the embodiments set forth herein ; rather , these embodiments are provided so that this disclosure will be thorough and complete . referring now to fig3 a - 3 c there is shown an example embodiment of a sleeve 16 adapted and configured for use on an arm of a patient . it is to be understood that although the description refers to an arm , the concepts and inventive attributes of the invention also apply for other body extremities , such as a patient &# 39 ; s leg , except that the “ sleeve ” would be configured in shape to accommodate the extremity of interest . the sleeve 16 is configured in a multi bladder or chamber arrangement and is formed of a material having an outer layer 1 preferably made of a two ply elastic material comprising an outer ply 2 preferably made of a woven urethane fabric embedded with loops 3 similar to those found in a velcro type material and an inner ply 4 formed of an elastic and non - gas permeable urethane sheet . the outer ply 2 and inner ply 4 are laminated together while under exposure to heat and pressure . the sleeve 16 also includes an inner layer 5 which is made from an elastic non - gas permeable material such as urethane . the two layers are suitably cut so that they can wrap around the arm when in use . elastic sheets 6 are positioned within the sleeve 16 to establish a plurality of sealed chambers 9 . the sheets 6 are sealed from edge to edge ( shown as 7 ) between the outer and inner layers to create multiple circumferential closed chambers . the two layers are sealed together at the sleeve periphery 8 . this structure creates multiple chambers 9 in the sleeve that are hermetically sealed and can be independently inflated . a suitable fitting 10 , such as barbed end , is also sealed to the outer layer of each chamber so that there is a passage or channel 11 to introduce air into the chamber . flaps 12 are positioned at the edge of the sleeve 16 and velcro sheets 13 , with “ hooks ”, are attached to the inner layer of the flaps . when the sleeve is positioned around the arm in a wraparound fashion , the velcro hooks on the flaps engage the outer layer which has corresponding velcro type loops for securing the sleeve 16 on the patients arm . the velcro type anchoring capability permits one sleeve size to fit snugly around a multitude of different sized arms . the sleeve 16 may also be held in place by adjustable straps or a fastener such as a zipper disposed along the length of the sleeve . the inner layer 5 is configured to come in contact with the patient &# 39 ; s skin when the sleeve 16 is wrapped around the arm and includes electrically conductive electrodes 14 for ift and biological impedance analysis . the electrodes 14 may be created by silk screening electrically conductive ink ( such as ag or au ) on the surface of the inner layer 5 that comes in contact with the patient &# 39 ; s skin or by attachment of an electrically conductive foil having an adhesive surface that will adhere to the inner layer . a suitable connector 15 in proximity to the flap edge is attached to the outer layer 1 of sleeve 16 to provide for making an electrical connection with the electrodes 14 . regarding certain lymphedema conditions , it may be desirable to create pressure points 17 on the arm with circumferential and longitudinal channels 18 for fluid flow and to allow “ breathing ” of the patient &# 39 ; s skin 19 . fig4 a - 4 b show a sleeve 22 which is a modification of the sleeve 16 for such purposes . sleeve 22 includes an elastic sheet 20 ( called an electrode flap ) which is attached to the upper edge of the sleeve 22 and includes embedded electrodes 14 . the electrode flap 20 is placed on the patient &# 39 ; s arm longitudinally so that the electrodes 14 come into electrical contact with the patient &# 39 ; s skin . an “ eggcrate ” foam sheet 21 is wrapped around the patient &# 39 ; s arm securing the electrode flap 20 to the arm . sleeve 22 encases the eggcrate foam sheet 21 and is wrapped around the patient &# 39 ; s arm and then is secured in place . preferably , eggcrate foam sheet 21 is covered with a suitable cloth to prevent shedding of the foam during sleeve use . multi - lumen tubing 63 , as shown in cross section in fig5 a - 5 b , connects the fittings 10 attached to the sleeve 16 and ultimately to the pump 40 ( fig6 c ) for inflation or deflation of the chambers 9 . the multi - lumen tubing cross section may be either circular or planar with hollow spaces or crevices 23 located between the lumens 24 . the electrical wiring 25 that connects the electrodes 14 to the biological impedance analysis and ift circuitry 38 may be routed through the crevices 23 as an efficient packaging and routing technique . the lumens 24 effectively act as a sheath for the electrical wiring 25 and thereby providing an enhanced safety feature . moreover , routing the electrical wiring 25 as described provides several other advantages such as protecting the wiring 25 from kinking & amp ; nicking during apparatus use and storage because the multi - lumen planar or circular cross - section offers more overall stiffness compared to individual tubes . a further advantage realized is enhanced ease of use since there is no clutter since a single multi - lumen tubing carries both the air and electrical wiring . the operation of the sleeves ( 16 and 22 ) is controlled by lymphedema control system ( lcs ) 28 . an example embodiment of the lymphedema control system 28 is shown in the block diagram of fig6 a . the lcs 28 comprises two main components ( modules ), an electronic controller ( ec ) 26 and pneumatic manifold 27 . an example block diagram of the electronic controller 26 is shown in fig6 b . a main component of electronic controller ( ec ) 26 is a processor 29 . the processor 29 may be an asic configured to carry out a preselected lymphedema treatment protocol and issue commands to the various components such as for example , to the pump 40 and the valves 43 - 52 in carrying out an inflation / deflation cycle or a general purpose computer programmed to carry out the algorithm shown in fig8 a - 8 e . the overall apparatus is powered by a low voltage dc power supply ( less than 48v ) 30 . this has several advantages such as protecting patient &# 39 ; s safety against electrical shock . the apparatus may also be powered by a battery such as a car or airplane battery or an electrical chair making the apparatus very portable thus giving enhanced mobility to patients . universal ac to dc converters such as used in laptop computers may also be used thus removing the problem of ac power supply incompatibility in different countries . ec 26 has an on - board battery backed real time clock ( rtc ) 31 , memory 32 , secure digital card ( sdc ) 33 , an audio processor 34 with a buzzer / speaker , a keypad 35 , a display 36 and wired and wireless communication 37 , biological impedance measurement and ift circuitry 38 and input / output ( i / o ) circuitry 39 . rtc 31 keeps track of time as well as the current day and date . rtc 31 is also used to log the frequency , duration and time / day of the lymphedema treatment and to set an alarm to remind the patient that a lymphedema treatment is due . multiple alarms may be set in a 24 hour period . rtc 31 also provides a reminder for the equipment service schedule times and total use time . the flash memory 32 is used to store patient information ( name , id no ., etc ), the patient treatment profile / protocol ( such as pressure profile of the various chambers , inflation sequence of the chambers , dwell time between each chamber — the time interval before starting to inflate the next chamber , rate of inflation of the chambers , number of cycles a sleeve is pressurized / inflated and depressurized / deflated for different sleeves used for an arm or leg , etc . sdc 33 may be used to transfer data from the apparatus to a physician without the necessity of having to take the apparatus to the physician &# 39 ; s office . the sdc 33 may be programmed by a physician to create a new treatment protocol as the lymphedema treatment progresses . ec 26 also includes the capability to store multiple treatment protocol for a patient such as one treatment protocol for the morning and a different treatment protocol for the evening . audio processor 34 provides audible information regarding the current lymphedema treatment , alarm triggers and conditions and instructions about the use of the apparatus . a keypad 35 integrated into the apparatus permits entry of various commands such as starting and stopping the lymphedema treatment , accessing the status of the apparatus and the lymphedema treatment and adjusting the audio volume , as mere examples . however , keypad 35 does not permit modification of the treatment protocol variables . a display 36 attached to the device displays visual information about the lymphedema treatment status , treatment parameters , alarm conditions , etc . ec 26 also has wired and wireless communication interfaces ( such as rs232 , rs485 , usb , lin ) to enable communication with an additional computer or pda . a graphical user interface ( gui ) ( not shown ) which is only accessible by service technicians permits reading , setting and modifying various hardware related parameters of the lcs 28 such as the number of chambers in the sleeve to be used , pressure sensors calibration , parameters related to the servo control of the pressure in chambers . another gui , only accessible to a physician and lymphedema therapy specialists permits adding , deleting and changing the treatment protocols . the wireless interface ( such as zigbee or proprietary protocols ) allows the use of a handheld remote control which can initiate all the commands available using of the keypad . this makes the apparatus very easy to use since the apparatus does not have to be within physical reach of the patient . a hand held remote can also undertake the same functions as keypad 35 , display 36 and audio processing 34 . ec 26 includes circuitry 39 to turn all the valves and pump on and off as desired as well as circuitry ( 39 ) to monitor pressure transducers that measure pressure in each chamber . ec 26 further includes circuitry 38 that provides for application of low voltage ac / dc , pulsed and non - pulsed prescribed electrical signals to the electrodes 14 embedded into the sleeve 16 that come in contact with the skin of the patient . a suitable conductive gel may be applied to the skin of the patient before the sleeve is attached so as to provide good electrical contact between electrodes 14 and the patient &# 39 ; s skin . the gel provides for enhanced interferential therapy applied to the extremity to which the sleeve 16 is wrapped around . the ec 26 provides performance of quantitative biological impedance measurements to monitor the effectiveness of compression and interferential therapies and assessment of the lymphedema condition . a block diagram of a pneumatic manifold 27 is shown in fig6 c . the output port 63 of a pneumatic pump 40 is attached to a manifold duct 67 . the input port 64 of the pump 40 is pneumatically connected to a particulate filter 41 and a muffler 42 . the particulate filter 41 is configured to prevent any particulate matter from entering the manifold 27 and the muffler 42 is configured to minimize any noise generated by the air flow to the manifold 27 . a two port , normally closed solenoid valve , identified as inflation / deflation ( i / d ) valve 43 is positioned between the pump 40 through duct 67 and the first chamber ( chn 1 ) of the sleeve 16 or sleeve 22 as the case may be . in a similar arrangement , i / d valves 44 - 50 are positioned between the pump 40 through duct 67 and sleeve chambers chn 2 - 8 , respectively . although an eight chamber sleeve has been described herein , it is to be understood that the number of channels , greater than one , is a design choice and may be altered depending upon use considerations . as discussed and shown in fig6 c , one port of i / d valve 43 is pneumatically connected to duct 67 in the manifold and the other port of i / d valve 43 is connected to duct 68 in the manifold which is pneumatically connected to chn 1 of sleeve 16 . in a similar arrangement , i / d valves 44 - 50 are connected to ducts 69 - 75 respectively which in turn are pneumatically connected to sleeve chn &# 39 ; s 2 - 8 , respectively . the i / d valve of each sleeve chamber 9 permits inflation / deflation of the respective sleeve chamber . a temperature compensated pressure transducer 54 is pneumatically connected to duct 68 . duct 68 in turn , is connected to chn 1 of sleeve 16 through a multiport connector 62 and multi - lumen tubing 63 . pressure transducer 54 permits monitoring of the pressure inside chamber 1 ( chn 1 ) so that ec 26 may cause the respective chamber pressure to be maintained at its prescribed value during a treatment protocol . in a similar arrangement pressure transducers 55 - 61 are connected to ducts 69 - 75 respectively for monitoring the pressure in chn &# 39 ; s 2 - 8 , respectively . also in a similar arrangement ducts 69 - 75 are connected , through multiport connector 62 to multi - lumen tubing 63 which connects to chn &# 39 ; s 2 - 8 , respectively . a two port , normally closed purge valve 51 is also pneumatically connected to manifold 27 . the purge valve 51 has a valve orifice , through which air flows , that has a cross - sectional area about 5 times larger than the cross - sectional area of the orifice of i / d valve 43 . accordingly , the purge valve 51 is capable of providing rapid discharge of air in the manifold 27 to the ambient environment . as noted , one port of the purge valve 51 is pneumatically connected to the duct 67 of manifold 27 while the other port of the purge valve discharges into the ambient environment 76 . under the control of ec 26 , the purge valve 51 provides for rapid and complete deflation of the sleeve chambers . a two port , normally closed tuning valve 52 , is also pneumatically connected to the manifold 27 . the cross - sectional area of the tuning valve orifice is about 5 times smaller than the cross - sectional area of the orifice of i / d valve 43 . the tuning valve 52 provides for removal of small amounts of air from the sleeve chamber / s to adjust the air pressure in the chamber / s to a prescribed value . the tuning valve 52 , due to its small orifice , provides for better control of the amount of air removed from the sleeve chamber / s compared to purge valve 51 . a mechanical over - pressure relief valve 53 is pneumatically connected the manifold 27 . the input port 65 of the over - pressure relief valve 53 is pneumatically connected to duct 67 and the output port 66 of the over - pressure relief valve 53 discharges into the ambient environment 76 . the over - pressure relief valve 53 provides for a fail - safe operation in cases of malfunction of the pneumatic system . another example embodiment of the lcs 28 is shown in fig7 a . the embodiment shown in fig7 a comprises two main components ( modules ), namely , remote unit 77 and electro - pneumatic module 78 ( epm ). an example electrical block diagram of the remote unit 77 is shown in fig7 b . the heart of the remote unit 77 is a processor ( cpu ) 79 powered by a battery 80 . it also has an on - board battery backed real time clock ( rtc ) 81 , memory 82 , an audio processor 83 with audio processing capability using a buzzer and speaker , a keypad 84 , a display 85 and a wired & amp ; wireless communication module 86 to interface with a computer and the epm &# 39 ; s . when communicating with a computer , remote unit 77 acts as a “ slave ” to the computer ( master ) and when communicating with epm modules , the remote unit 77 acts as a master . a block diagram of the epm 78 is shown in fig7 c . the heart of an epm is an integrated miniature air pump 87 and a two - port normally closed purge valve 88 driven by elastomers called electroactive polymers ( epam ). epam is currently available from artificial muscle corporation of redwood city , calif . also included in this embodiment is a mechanical over - pressure relief valve 89 assembly connected to each sleeve chamber . the pump output port 91 , an input port of the purge valve 88 and input port 93 of the over - pressure relief valve 89 are pneumatically connected directly to a sleeve chamber . input port 92 of the air pump 87 , an output port of the purge valve 88 and an output port 94 of the over pressure relief valve 89 discharge into the ambient environment 76 . a pressure transducer 90 installed between a sleeve chamber and air pump 87 measures the pressure in a respective sleeve chamber . the pump 87 and the purge valve 88 are under the control of a local cpu ( processor ) and its associated circuitry assembly 95 . biological impedance measurement and ift circuitry 96 are also located on this assembly and are controlled by the local cpu . wired and wireless communication interface 97 located on the assembly provides for communication between the remote unit 77 and an epm 78 . an external power source 98 provides power to all the electronics , valves and pumps of an epm . in this embodiment , i / d valves are not required because each sleeve chamber is pressurized individually by its own epm pump instead of sharing a common pump . each sleeve chamber has its own deflation / pressure adjustment valve rather than sharing common purge and tuning valves . this arrangement permits inflation or deflation of any chamber concurrently with other chambers . for example , while one sleeve chamber is being inflated , another sleeve chamber may be deflating to adjust its pressure concurrently or two chambers may be inflating concurrently independently of each other . each sleeve chamber has its own epm installed on the sleeve . all epm &# 39 ; s are under the direct control of the remote unit 77 which performs the same functions as the lcs 28 of the earlier described embodiment , except the sleeve control functions are performed by epms . any epm can perform biological impedance measurement and ift functions depending on which epm is connected to the electrodes 14 . each epm has its own id number ( set by switches or programmed into the cpu ) which is same as the respective sleeve chamber number . this allows the remote unit 77 to communicate with each epm directly . electroactive polymer artificial muscle ( epam ) has significant differences from not only conventional electromagnetic actuators but from other technologies like piezo - electric crystals and shape memory alloys . a significant advantage that epam has over electromagnetic actuators is its energy density , that is , more energy created for the mass of the actuator itself . compared to shape memory alloy and piezo electric technology , epam &# 39 ; s have a significant direct displacement advantage . while shape memory alloy and piezo - electric technology might achieve a 1 % direct displacement , epam actuators can reach 20 % or more displacement levels over long life cycles . compared to conventional electromagnetic motors , epam &# 39 ; s have a significant advantage in power density . epam &# 39 ; s will provide the same level of power as an electromagnetic motor device but with a much smaller and lower weight form factor , much like the human muscle . the epam basic architecture is made up of a film of an elastomer dielectric material that is coated on both sides with another expandable film of a conducting electrode . when voltage is applied to the two electrodes , a maxwell pressure is created on the elastic dielectric polymer layer . the elastic dielectric polymer acts as an incompressible fluid which means that as the electrode pressure ( voltage ) causes the elastomer dielectric film to become thinner , the dielectric film expands in planar directions and thus provides mechanical actuation and motion . advantageously , epam &# 39 ; s can be patterned to pinpoint actuation in multiple locations . before commencing ct and / or ift , a quantitative measurement of the biological impedance of the extremity afflicted with lymphedema is performed using a bio - impedance ( biological impedance ) analysis ( bia ) methodology . bia is based on two important concepts namely : a human body contains water and conductive electrolytes ( collectively “ fluids ”) and the electrical impedance of a body part such as an extremity ( limb ) is related to the length and cross - sectional area of the extremity , as well the frequency of the electrical current applied to the extremity . for the most part , body fluids conduct the electrical current that passes through a limb . fluids are present both inside a human body cell , called intracellular fluid and outside the human body cells , called extracellular fluid . at low frequency , electrical current passes through the extracellular fluid and does not penetrate the cell membrane . at high frequency , however , electrical current passes through both the intracellular and extracellular fluids . by using a fixed strength electrical current , the bio - impedance of a limb can be measured which is inversely proportional to the amount of fluid in the limb . accordingly , as the fluid in the limb decreases , the bio - impedance will increase . bio - impedance analysis may be performed by any of one of three methods . single frequency analysis is generally performed at about 50 khz . at this frequency , the electrical current passes through both the intracellular and extracellular fluids . based on this measurement total body water can be calculated . however , since the current passes through both the intracellular and extracellular fluids , it is not possible to determine the intracellular fluid alone . the results are based on predictive algorithms derived from healthy subjects . in multi - frequency bio - impedance analysis , the impedance is measured at no greater than seven different frequencies . empirical linear regression analysis is then used to derive the impedance values . in bio - impedance spectroscopy , impedance is measured at 256 different frequencies and mathematical modeling is used to calculate the impedance values . a data entry listing for an example treatment protocol ( profile ) having either compression therapy or interferential therapy parameters or both loaded into the memory of the ec 26 is shown in appendix a . multiple protocol &# 39 ; s may be stored in the memory of the ec 26 for rapid access and use . for the present discussion , the input data for the sleeve chambers will refer to chamber one ( chn 1 ) of the sleeve with the understanding that the other chambers of the sleeve have similar data entries . a thorough description of the execution of a lymphedema protocol with reliance on a similar entered data listing will be described below with reference to fig8 a - 8 e . the compression therapy ( ct ) parameters include pressure set point for all the chambers ( 101 ), sequence of inflation of the chambers ( 102 ), dwell ( pause ) time ( 103 ) for each chamber ( the time interval after inflating a chamber to a pressure set point before starting inflation / deflation of the next chamber ( s ), sequence end delay ( 105 ) ( time interval after inflating all the chambers and start of the deflation cycle ), sleeve deflation period after the end of inflation cycle ( 115 ), “ end of treatment ” parameters ( 104 ) which includes the number of inflation / deflation cycles to occur for the treatment , a fixed amount of time for the treatment , attainment of a prescribed percentage of the original measured biological impedance , attainment of a fixed value of impedance value or a combination of the above parameters . the lymphedema treatment is terminated when any of the “ end of treatment ” parameters are met . any sleeve chamber can be set to stay inflated ( 106 ) throughout the treatment . this is especially true for the chamber at the proximal end of the sleeve when wrapped around a body extremity such as a hand or foot . since a foot , for example , is at the distal end of a patient &# 39 ; s leg , lymph fluid can only go out from and away from the foot along the patient &# 39 ; s leg towards the groin , where the distal end of the sleeve is located and thus there is no need to deflate the sleeve chamber at its proximal end to permit the lymphatic fluid from entering the patient &# 39 ; s foot . the product of a chamber pressure set point and corresponding dwell time is generally maintained at a constant value for all the chambers so that approximately same amount of lymphatic fluid moves along in the treated limb from chamber to chamber during inflation . these programmable parameters also provide the versatility of programming monotonically decreasing , monotonically increasing or constant pressure gradients in the sleeve . the ift parameters include the amplitude of applied voltage ( ac / dc ) ( 107 ), pulse duration ( 108 ), pulse rate ( 109 ) and “ end of treatment ” parameters which are same as for the ct . the treatment protocol also contains treatment related parameters such as protocol number ( 111 ), protocol name ( arm , leg , etc . )( 110 ) and patient related parameters such as name ( 112 ), social security number ( ssn ) ( 113 ), etc . sleeve related parameters include the number of chambers ( 114 ). referring now to fig8 a - 8 e , there is shown an example flow diagram of a program , preferably cast in firmware that controls the operation of lcs 28 . upon application of power to the lcs 28 ( system power switch on ), the cpu and the support circuitry 29 the ec 26 is reset , all the i / d valves 43 - 51 are set to closed position , and the pump 40 is in off condition . lcs 28 goes into a standby mode 121 which is shown on the display 36 as well as an audio message “ power on ” is announced . in the standby mode 121 , the treatment protocols may be loaded , erased , modified or an established treatment protocol can be set to a default treatment protocol for a particular limb positioned on sleeve 16 . the default treatment protocol is executed when the treatment start button is pressed either from the remote control 99 or keypad 35 . during the standby mode 121 , the purge cycle 122 can be initiated from the keypad 35 ( all the i / d valves 43 - 52 are opened ) thus removing any air from the sleeve which facilitates mounting the sleeve on the extremity to be treated . when a start command is pressed from the keypad 35 , an autozero cycle 123 is started . the display 36 displays the notation “ starting treatment ” and the audio processor 34 announces “ start of treatment ”. in the auto zero cycle 123 , all i / d valves 43 - 52 are opened so as to deflate all the sleeve chambers thus equalizing the pressure inside and outside sleeve 16 . the pressure transducers 54 - 61 continuously monitor ( measure ) the pressure inside each of the sleeve chamber ( s ) 9 . when the measurements of all the pressure transducers 54 - 61 ( after analog to digital nd conversion ) becomes stable and meet programmed criteria , the pressure inside and outside the sleeve 16 is indicated as becoming equal . at this time , all the pressure transducer ( 54 - 61 ) measurements are equivalent to measuring “ zero ” pressure . these values are stored in memory 32 and used to measure the correct pressure inside the sleeve chambers . this procedure compensates for any zero drift of the pressure transducers due to aging and temperature and electronic component drift . after completion of the auto zero mode 123 , all i / d valves 43 - 52 are closed . if a pressure transducer stability criteria is not met , the apparatus goes into an alarm mode 125 and lymphedema treatment is aborted . upon completion of the auto zero mode 123 , a lymphedema treatment cycle commences and depending upon the selected extremity , at 126 for an arm or at 127 for a leg with ct and ift also starting according to the current active protocol . for ct , inflation cycle 128 commences and assuming that sleeve chamber 1 ( chn 1 ) is pressurized first ( as defined in appendix a ), the i / d valve 43 is opened and the pneumatic pump 40 is started to provide pressurized air to chn 1 . the pressure transducer 54 located between the i / d valve 43 and the corresponding chn 1 of the sleeve monitors the chamber pressure . in one embodiment , the pressure transducer 54 is located close to i / d valve 43 and there is a measureable pressure drop between the pressure transducer 54 and the sleeve chn 1 due to the resistance , caused by friction , to the air flow through manifold duct 68 and the multi - lumen tubing 63 . it is to be noted , that the longer the tubing 63 , the higher the pressure loss . initially the pressure inside chn 1 is zero . therefore , the pressure reading from the pressure transducer 54 at the very beginning of the inflation cycle is equal to the pressure drop through the tubing 63 for chn 1 for the given flow capacity of the pump 40 . this dynamic pressure drop is measured for all the chambers ( channels ) ( 1 - 8 ) during the first inflation cycle of all the chambers and stored in memory 32 . this dynamic pressure drop parameter is used as an input parameter to a commonly available proportional integral derivative algorithm ( pid ) stored and performed in ec 26 to compensate for any error in pressure measurement in order to achieve the programmed pressure in the sleeve chambers , in the least amount of time without either over or under shooting the programmed pressure value . this automatic compensation of the dynamic pressure drop through the tubing 63 for each sleeve chamber alleviates the need to manually set these values and results in maintaining accurate pressure values in the sleeve chambers . alternatively , pressure transducers ( 54 - 61 ) may be mounted very close or on the respective sleeve chambers . in such case , the pressure drop between a pressure transducer and the respective sleeve chamber is negligible , if any , but requires that the electrical conductors must be provided between the pressure transducers on the sleeve ( 16 , 22 ) to the ec 26 . as has been previously described , sleeve ( 16 , 22 ) may be formed of flexible elastomeric material . accordingly , when a sleeve chamber is pressurized to its programmed value ( set point ), the chamber applies a force to the adjacent chamber . this force causes the volume of the adjacent chamber to decrease slightly , especially if the adjacent chamber is pressurized , resulting in pressure increase above its set point . there is also a pressure drop in the adjacent chamber due to cooling of the hot air that was caused by adiabatic heating of the air during the pressurization process . these two factors may cancel each other or there may be some plus or minus pressure change depending upon such factors as the size and design of the sleeve and the amount of adiabatic heating occurring during the pressurization process . during a delay interval ( pause time 103 ) and after a sleeve chamber is pressurized , the ec 26 causes adjustment of the pressure of the adjacent chamber ( s ) to their respective set points ( either by deflating the chamber ( s ) or by pumping more air in the chamber ( s ). however , simultaneous inflation and deflation of the chambers can not be done . the difference in the set point and the actual pressure in a chamber determines the priority of pressure adjustment during the dwell time 103 , where the higher the difference , the higher the priority for pressure adjustment for the respective chamber . this continuous pressure control / adjustment of the chambers provides the capability of a monotonically decreasing , monotonically increasing or a constant pressure gradient along the length of the sleeve as defined by treatment protocol . at the conclusion of inflation cycle 128 , a purge cycle 129 commences wherein all chambers but chn 1 are deflated . subsequent to the completion of deflation of the desired chambers , the treatment termination criteria is checked . if any one of the treatment termination criteria has not been met , inflation cycle 128 is repeated . if any one of the treatment termination criteria has been met , purge cycle 130 commences wherein all of the chambers including chn 1 are deflated . at the end of purge cycle 130 , ec 26 commands that the lcs 28 goes into standby mode 121 . at block 124 , the ift and biological impedance measurement cycle commences . the first biological impedance measurement value is stored in memory 32 and used as a reference and the ift cycle 131 commences . the ift cycle 131 is undertaken with the preselected electrical pulse parameters for ift such as amplitude , duration and frequency such pulse signals being applied to the sleeve electrodes 14 . the measured biological impedance values are then compared and displayed and when the treatment termination criteria is met , ift is stopped and the device goes into standby mode . if ift is being undertaken in conjunction with ct , any alarm in ct will also terminate ift . fig9 shows the pressure - time profile in the chambers of the sleeve during compression therapy treatment cycle . a time pressure graphical representation of the inflation and deflation cycle for the eight chambers of the sleeve ( 16 , 22 ) is shown in fig9 . at to , the initial starting time for the compression therapy , all of the sleeve chambers are completely deflated . at such time , ec 26 commands that inflation of chamber one ( chn 1 ) commences . at t 1 , the pressure in chn 1 reaches its prescribed value ( set point ) and inflation of chn 1 , ceases . a pause or delay interval then is commanded from between t 1 to t 2 where no further inflation activity is undertaken . at t 2 , inflation of chn 2 commences while chn 1 is maintained at its prescribed pressure set point . once the pressure in chn 2 reaches its prescribed value , inflation of chn 2 ceases . any variation of the pressure in chn 1 , as shown at t 3 , resulting from the inflation of chn 2 is compensated by ec 26 so as to maintain chn 1 at its prescribed pressure set point . subsequent to the delay interval between t 3 and t 4 , inflation of chn 3 commences until the pressure in chn 3 reaches its prescribed value , while the pressures in chn 1 and chn 2 are maintained at their respective prescribed values . the above process continues in a like manner , including checking the chambers for any changes in their pressure vale due to pressurization of adjacent chambers , until all the chambers are inflated which terminates at time t 6 . at t 6 , the treatment termination criteria are examined and if none of the criteria are satisfied all chambers , except chn 1 , are deflated between t 6 and t 7 . the entire process , commencing with inflation of chn 2 , is repeated . upon completion of the entire repeated process , the termination criteria is again examined ( at t 9 ) and if any one of the criteria is satisfied , all the chambers , including chn 1 are deflated at t 10 , and the lymphedema treatment session is terminated . at end of a lymphedema treatment session , all the operational parameters are logged into memory 32 so that the effectiveness of the therapies can be ascertained . depending on the embodiment , certain acts , events , or functions of any of the methods described herein can be performed in a different sequence , may be added , merged , or elimnated ( e . g ., not all described acts or events are necessary for the practice of the method ). moreover , in certain embodiments , acts or events may be performed concurrently , e . g ., through multi - threaded processing , interrupt processing , or multiple processors , rather than sequentially . the various illustrative logical blocks , modules , circuits , and algorithm steps described in connection with the embodiments disclosed herein may be implemented as electronic hardware , computer software , firmware or combinations thereof . to clearly illustrate this interchangeability of hardware and software , various illustrative components , blocks , modules , circuits , and steps have been described above generally in terms of their functionality . whether such functionality is implemented as hardware or software depends upon the particular application and design constraints imposed on the overall apparatus . the described functionality may be implemented in varying ways for each particular application , but such implementation decisions should not be interpreted as causing a departure from the scope and intent of the disclosure . the various illustrative logical blocks , modules , and circuits described in connection with the embodiments disclosed herein may be implemented or performed with a general purpose processor , a digital signal processor ( dsp ), an application specific integrated circuit ( asic ), a field programmable gate array ( fpga ) or other programmable logic device , discrete gate or transistor logic , discrete hardware components , or any combination thereof designed to perform the functions described herein without departing from the spirit of the invention . a general purpose processor may be a microprocessor , but in the alternative , the processor may be any conventional processor , controller , microcontroller , or state machine . a processor may also be implemented as a combination of computing devices , e . g ., a combination of a dsp and a microprocessor , a plurality of microprocessors , one or more microprocessors in conjunction with a dsp core , or any other such configuration . the lyphedema treatment method or algorithm described in connection with the embodiments disclosed herein may be embodied directly in hardware , in a software module executed by a processor , or in a combination thereof without departing from the spirit of the invention . a software module may reside in ram memory , flash memory , rom memory , eprom memory , eeprom memory , registers , hard disk , a removable disk , a cd - rom , or any other form of storage medium known in the art . an exemplary storage medium is coupled to the processor such the processor can read information from , and write information to , the storage medium . in the alternative , the storage medium may be integral to the processor . the processor and the storage medium may reside in an asic . the asic may reside in a user terminal . in the alternative , the processor and the storage medium may reside as discrete components in a user terminal . with regard to the use of a processor , the flow chart or algorithm disclosed at least in fig8 a - 8 e provides more than adequate information for one skilled in the art to program such processor to perform the lymphedema treatment method disclosed herein . while the above detailed description has shown , described , and pointed out novel features as applied to various embodiments , it will be understood that various omissions , substitutions , and changes in the form and details of the device or process illustrated may be made without departing from the spirit of the disclosure . as will be recognized , certain embodiments of the inventions described herein may be embodied within a form that does not provide all of the features and benefits set forth herein , as some features may be used or practiced separately from others . the scope of the inventions is indicated by the appended claims rather than by the foregoing description . all changes which come within the meaning and range of equivalency of the claims are to be embraced within their scope .
an apparatus and method for treatment of patients suffering from lymphedema manifested at various locations of the human body . the apparatus includes a multiple chamber sleeve to be positioned in a wrap around fashion on a body extremity to be treated by compression therapy . the chambers are sequentially inflated and maintained so until all chambers are inflated and then all the chambers are simultaneously deflated so as to move edema fluids out of the afflicted area and to stimulate the lymphatic system . the apparatus also includes the capability to measure the biological impedance of the extremity under treatment as a treatment parameter as well as applying interferential therapy either alone or in combination with compression therapy . advantageously , the sleeve chambers capture pressurized air when applied thereto , at designated locations , so as to form air pockets that can selectively apply isolated points of pressure , and in combination with the application of electrical current to a medical patient &# 39 ; s affected area , provide effective lymphedema therapy without disrupting normal vascular and lymphatic functioning .