although those of ordinary skill in the art will readily recognize many alternative embodiments , especially in light of the illustrations provided herein , this detailed description is exemplary of the preferred embodiment of the present invention , the scope of which is limited only by the claims that are drawn hereto . the present invention is a vacuum assisted system for stimulating the healing of tissue . referring now to fig1 in particular , there is illustrated the primary components of a system that operates in accordance with the present invention . the present invention 10 includes a foam pad 11 for insertion substantially into a wound site 12 and a wound drape 13 for sealing enclosure of the foam pad 11 at the wound site 12 . the foam pad 11 may be comprised of a polyvinyl alcohol ( pva ) open cell polymer material , or other similar material having a pore size sufficient to facilitate wound healing . a pore density of greater than 38 pores per linear inch is preferable . a pore density of between 40 pores per linear inch and 50 pores per linear inch is more preferable . a pore density of 45 pores per linear inch is most preferable . such a pore density translates to a pore size of approximately 400 microns . addition of an indicating agent , such as crystal violet , methylene blue , or similar agents known in the art causes a color change in the foam 11 when in the presence of a bacterial agent . as such , a user or health care provider can easily and readily ascertain if an infection is present at the wound site 12 . it is contemplated that the indicating agent may also be placed in line of the conduit 16 , between the wound site 12 and the canister 18 . in such a configuration ( not shown ), the presence of bacterial contaminants in the wound site 12 , could be easily and readily ascertained without disturbing the wound bed , as there would be a nearly immediate color change as bacterially infected wound exudates are drawn from the wound site 12 and through the conduit 16 during application of negative pressure . it is also contemplated that the foam pad 11 may be coated with a bacteriostatic agent . addition of such an agent , would serve to limit or reduce the bacterial density present at the wound site 12 . the agent may be coated or bonded to the foam pad 11 prior to insertion in the wound site , such as during a sterile packaging process . alternatively , the agent may be injected into the foam pad 11 after insertion in the wound site 12 . after insertion into the wound site 12 and sealing with the wound drape 13 , the foam pad 11 is placed in fluid communication with a vacuum source 14 for promotion of fluid drainage and wound healing , as known to those of ordinary skill in the art . the vacuum source 14 may be a portable electrically powered pump , or wall suction as commonly provided in medical care facilities . according to the preferred embodiment of the present invention , the foam pad 11 , wound drape 13 , and vacuum source 14 are implemented as known in the prior art , with the exception of those modifications detailed further herein . the foam pad 11 preferably comprises a highly reticulated , open - cell polyurethane or polyether foam for effective permeability of wound fluids while under suction . the pad 11 is preferably placed in fluid communication , via a plastic or like material conduit 16 , with a canister 18 and a vacuum source 14 . a first hydrophobic membrane filter 20 is interposed between the canister 18 and the vacuum source 14 , in order to prevent wound exudates from contaminating the vacuum source 14 . the first filter 20 may also serve as a fill - sensor for canister 18 . as fluid contacts the first filter 20 , a signal is sent to the vacuum source 14 , causing it to shut down . the wound drape 13 preferably comprises an elastomeric material at least peripherally covered with a pressure sensitive adhesive for sealing application over the wound site 12 , such that a vacuum seal is maintained over the wound site 12 . the conduit 16 may be placed in fluidic communication with the foam 11 by means of an appendage 17 that can be adhered to the drape 13 . according to the preferred method of the present invention , a second hydrophobic filter 22 is interposed between the first filter 20 and the vacuum source 14 . the addition of the second filter 22 is advantageous when the first filter 20 is also used as a fill sensor for the canister 18 . in such a situation , the first filter 20 may act as a fill sensor , while the second filter 22 further inhibits contamination of wound exudates into the vacuum source 14 . this separation of functions into a safety device and a control ( or limiting ) device , allows for each device to be independently engineered . an odor vapor filter 23 , which may be a charcoal filter , may be interposed between the first filter 20 and the second filter 22 , in order to counteract the production of malodorous vapors present in the wound exudates . in an alternate embodiment ( not shown ), the odor vapor filter 23 may be interposed between the second hydrophobic filter 23 and the vacuum source 14 . a second odor filter 15 may be interposed between the vacuum source 14 and an external exhaust port 25 , in order to further reduce the escape of malodorous vapors from the present system . a further embodiment allows for first 20 and second filters 22 to be incorporated as an integral part of the canister 18 to ensure that the filters 20 , 22 , at least one of which are likely to become contaminated during normal use , are automatically disposed of in order to reduce the exposure of the system to any contaminants that may be trapped by the filters 20 and 22 . a means for sampling fluids may also be utilized by providing a resealable access port 24 from the conduit 16 . the port 24 is positioned between the distal end 16 a of the conduit 16 and the proximal end 16 b of the conduit 16 . the port 24 , as further detailed in fig2 a and 2 b , is utilized to allow for sampling of fluids being suctioned from the wound site 12 . although the port 24 is shown as an appendage protruding from the conduit 16 , it is to be understood that a flush mounted port ( not shown ) will serve an equivalent purpose . the port 24 includes a resealable membrane 26 that after being punctured , such as by a hypodermic needle , the seal is maintained . various rubber - like materials known in the art for maintaining a seal after puncture can be utilized . the process by which wound fluids are sampled , utilizing the present invention , comprises penetrating the membrane 26 with a fluid sampler 28 , such as a hypodermic needle or syringe . the sampler 28 is inserted through the membrane 26 and into the port 24 until it is in contact with wound fluids flowing through the inner lumen 30 of the conduit 16 . as illustrated in fig2 b , and further described in u . s . pat . no . 6 , 142 , 982 , issued to hunt , et al . on may 13 , 1998 , and whose reference is incorporated herein as though fully set forth , the inner lumen 30 may be surrounded by one or more outer lumens 31 . the outer lumens 31 may serve as pressure detection conduits for sensing variations in pressure at the wound site 12 . in an alternative embodiment ( not shown ), the outer lumen or lumens 31 may act as the negative pressure conduit , while the inner lumen 30 may act as the pressure detection conduit . in the present invention , the fluid sampling port 24 , communicates only with the inner lumen 30 , so as not to interfere with pressure detection that may be conducted by the outer lumens 31 . in an alternate embodiment ( not shown ) in which the outer lumen 31 serves as the negative pressure conduit , the fluid sampling port 24 communicates with the outer lumen 31 . the vacuum source 14 may consist of a portable pump housed within a housing 32 , as illustrated in fig3 a and 3 b . a handle 33 may be formed or attached to the housing 32 to allow a user to easily grasp and move the housing 32 . according to the preferred embodiment of the present invention , a means for securing the housing 32 to a stationary object , such as an intravenous fluid support pole for example , is provided in the form of a clamp 34 . the clamp 34 , which may be a g - clamp as known in the art , is retractable , such that when not in use is in a stored position within a recess 36 of the housing 32 . a hinging mechanism 38 is provided to allow the clamp 34 to extend outward from the housing 32 , to up to a 90 degree angle from its stored position . an alternative embodiment ( not shown ) allows the clamp 34 to be positioned at up to a 180 degree angle from its stored position . the hinging mechanism 38 is such that when the clamp 34 is fully extended , it is locked in position , such that the housing 32 is suspended by the clamp 34 . a securing device 40 , such as a threaded bolt , penetrates through an aperture 42 of the clamp 34 , to allow the clamp 34 to be adjustably secured to various stationary objects of varying thickness . alternatively , the securing device 40 , may be comprised of a spring actuated bolt or pin , that is capable of automatically adjusting to various objects , such as intravenous fluid support poles , having varying cross - sectional thicknesses . the present invention also allows for management of a power supply to the vacuum source 14 , in order to maximize battery life when the present invention is utilizing a direct current as its power supply . in the preferred embodiment , as illustrated in the flow chart of fig4 a , a motor control 44 determines if the actual pressure is less than or equal to a target pressure 46 . if the actual pressure is less than the target pressure , a tentative motor drive power required to reach the target pressure is calculated 48 . if the tentative motor drive power required to reach the target pressure is greater or equal to the stall power 49 , the tentative motor drive power is actually applied to the motor 50 . if the actual pressure is greater than the target pressure , the tentative motor drive power is decreased and a determination is made as to whether additional power is needed to overcome the stall power 52 . if it is determined that the tentative power is inadequate to overcome the stall power , the tentative power is not supplied to the motor 54 . if the tentative power is adequate to overcome the stall power , the tentative power is actually applied to the motor 50 . the motor control 44 functions as a closed loop system , such that the actual pressure is continuously measured against the predetermined target pressure . the advantage of such a system is that it prevents power from being supplied to the motor when it is not necessary to maintain the target pressure specified for v . a . c therapy . accordingly , battery life is extended because power is not needlessly used to power the motor when it is not necessary . battery life is further extended , as illustrated in the flow chart shown in fig4 b , by providing a means , such as an integrated software program in a computer processor , for automatically disengaging a backlight of the visual display 19 of the present invention 10 ( as seen in fig3 b ). user input of information 55 , such as target pressure desired , or duration of therapy , activates 57 a backlight of the visual display 19 shown in fig3 b . user input 55 may also be simply touching the visual display 19 , which may be a touch activated or a pressure sensitive screen as known in the art . activation of an alarm 55 may also activate 57 the backlight of the display 19 . an alarm may be automatically activated if an air leak is detected at the wound site 12 . such a leak may be indicated by a drop or reduction in pressure being detected at the wound site 12 . the backlight remains active until a determination is made as to whether a preset time interval has elapsed 58 . if the time interval has not elapsed , the backlight remains active 57 . if the time interval has elapsed , the backlight is automatically extinguished 59 , until such time as the user inputs additional information , or an alarm is sounded 55 . referring now back to fig1 , battery life is further extended by means of a variable frequency pump drive system 80 , when the pump 14 , used in accordance with the present invention , is an oscillating pump . the pump drive system 80 consists of a pressure sensor 82 , a control system 84 , and a variable frequency drive circuit 86 . in the preferred embodiment the pressure sensor 82 measures the pressure across the pump , which is relayed to the control system 84 . the control system 84 determines the optimum drive frequency for the pump 14 given the pressure measured and relayed by the pressure sensor 82 . the optimum drive frequency for the pump 14 may be determined by the control system 84 either repeatedly or continuously . the control system 84 adjusts the variable frequency drive circuit 86 to drive the pump at the optimum frequency determined by the control system 84 . the use of the variable frequency pump drive system 80 allows the pressure of the pump 14 to be maximized . in tests on sample oscillating pumps , the maximum pressure achieved was doubled by varying the drive frequency by only 30 %. additionally , the system 80 maximizes flow rate over the extended frequency range . as a result , performance of the pump 14 is significantly improved over existing fixed frequency drive system pumps without increasing the pump size or weight . consequently , battery life is further extended , thus giving the user greater mobility by not having to be tethered to a stationary power source . alternatively , a similar performance level to the prior art fixed frequency drive system pumps can be achieved with a smaller pump . as a result , patient mobility is improved by improving the portability of the unit . the preferred embodiment also increases the stimulation of cellular growth by oscillating the pressure over time , as illustrated in the flow chart of fig5 . such an oscillation of pressure is accomplished through a series of algorithms of a software program , utilized in conjunction with a computer processing unit for controlling the function of the vacuum source or pump . the program is initialized when a user , such as a health care provider , activates the pulsing mode of the pump 60 . the user then sets a target pressure maximum peak value and a target pressure minimum peak value 62 . the software then initializes the pressure direction to “ increasing ” 63 . the software then enters a software control loop . in this control loop , the software first determines if the pressure is increasing 64 . if the actual pressure is increasing in test 64 , a determination is then made as to whether a variable target pressure is still less than the maximum target pressure 70 . if the variable target pressure is still less than the maximum target pressure the software next determines whether the actual pressure has equaled ( risen to ) the ascending target pressure 66 . if the actual pressure has attained the ascending target pressure , the software increments the variable target pressure by one interval 68 . otherwise , it refrains from doing so until the actual pressure has equaled the ascending target pressure . if the variable target pressure has reached the maximum target pressure in the test of block 70 the software sets the pressure direction to “ decreasing ” 69 and the variable target pressure begins to move into the downward part of its oscillatory cycle . the interval may be measured in mmhg or any other common unit of pressure measurement . the magnitude of the interval is preferably in the range of about 1 to 10 mmhg , according to the preference of the user . if the actual pressure is decreasing in test 64 , a determination is then made as to whether the variable target pressure is still greater than the minimum target pressure 74 . if the variable target pressure is still greater than the minimum target pressure the software next determines whether the actual pressure has attained ( fallen to ) the descending target pressure 76 . if the actual pressure has equaled the descending target pressure the software decrements the variable target pressure by one interval 72 . otherwise it refrains from doing so until the actual pressure has equaled the descending target pressure . if the variable target pressure has reached the minimum target pressure in the test of block 74 , the software sets the pressure direction to “ increasing ” 73 and the variable target pressure begins to move into the upward part of its oscillatory cycle . this oscillatory process continues until the user de - selects the pulsing mode . while the invention has been described herein with reference to certain preferred embodiments , these embodiments have been presented by way of example only , and not to limit the scope of the invention . accordingly , the scope of the invention should be identified only in accordance with the claims that follow .
a system for stimulating the healing of tissue comprises a porous pad positioned within a wound cavity , and an airtight dressing secured over the pad , so as to provide an airtight seal to the wound cavity . a proximal end of a conduit is connectable to the dressing . a distal end of the conduit is connectable to a negative pressure source , which may be an electric pump housed within a portable housing , or wall suction . a canister is positioned along the conduit to retain exudates suctioned from the wound site during the application of negative pressure . a first hydrophobic filter is positioned at an opening of the canister to detect a canister full condition . a second hydrophobic filter is positioned between the first filter and the negative pressure source to prevent contamination of the non - disposable portion of the system by exudates being drawn from the wound . an odor filter is positioned between the between the first and second hydrophobic filters to aid in the reduction of malodorous vapors . a securing means is supplied to allow the portable housing to be secured to a stationary object , such as a bed rail or intravenous fluid support pole . a means for automated oscillation of pressure over time is provided to further enhance and stimulate the healing of an open wound . a means for varying pump drive frequency and a means for managing a portable power supply are provided to increase battery life and improve patient mobility .