Abstract:
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.

Description:
FIELD OF THE INVENTION 
   This invention relates generally to tissue treatment systems. More particularly this invention relates to vacuum assisted treatment systems that aid in the healing of open wounds. 
   BACKGROUND OF THE INVENTION 
   Vacuum induced healing of open wounds has recently been popularized by Kinetic Concepts, Inc. of San Antonio, Tex., by its commercially available V.A.C.® product line. The vacuum induced healing process has been described in commonly assigned U.S. Pat. No. 4,969,880 issued on Nov. 13, 1990 to Zamierowski, as well as its continuations and continuations in part, U.S. Pat. No. 5,100,396, issued on Mar. 31 1992, U.S. Pat. No. 5,261,893, issued Nov. 16, 1993, and U.S. Pat. No. 5,527,293, issued Jun. 18, 1996, the disclosures of which are incorporated herein by this reference. Further improvements and modifications of the vacuum induced healing process are also described in U.S. Pat. No. 6,071,267, issued on Jun. 6, 2000 to Zamierowski and U.S. Pat. Nos. 5,636,643 and 5,645,081 issued to Argenta et al. on Jun. 10, 1997 and Jul. 8, 1997 respectively, the disclosures of which are incorporated by reference as though fully set forth herein. Additional improvements have also been described in U.S. Pat. No. 6,142,982, issued on May 13, 1998 to Hunt, et al. 
   In practice, the application to a wound of negative gauge pressure, commercialized by Assignee or its parent under the designation “Vacuum Assisted Closure” (or “V.A.C.®”) therapy, typically involves the mechanical-like contraction of the wound with simultaneous removal of excess fluid. In this manner, V.A.C.® therapy augments the body&#39;s natural inflammatory process while alleviating many of the known intrinsic side effects, such as the production of edema caused by increased blood flow absent the necessary vascular structure for proper venous return. As a result, V.A.C.® therapy has been highly successful in the promotion of wound closure, healing many wounds previously thought largely untreatable. 
   The frequency at which negative pressure is applied to the wound, as well as the frequency of the pressure change over time, has a direct impact on the rate of wound healing. A variation of pressure change over time, not provided by current vacuum assisted therapy devices, is thought to significantly increase the rate of wound healing. Similarly, a rapid return to normal activities for the patient receiving wound therapy, may also improve the rate of wound healing, as increased physical activity is often accompanied by increased vascular circulation, which in turn leads to improved blood flow at the wound site. One barrier to a return to normal activities is limited battery life, which is a result of the electrical power required to power existing vacuum assisted wound therapy systems. Additionally, frequent inspection of the wound site is required in order to ensure the wound is not becoming infected. However, a rapid return to normal activities must not preclude the precautions that must be utilized during use of vacuum assisted therapy to prevent inadvertent spillage of wound exudates from the canister, or entry of wound exudates into the pumping mechanism. 
   Additional limitations are associated with the use of fixed frequency oscillating pumps in the prior art. Such limitations are the result of the size of the pump required to maintain the desired negative pressure at the wound site, and/or a reduction in battery life due to the power required to operate the oscillating pumps. Oscillating pumps, as known in the art, are typically designed for limited operating conditions. For example, to maximize low pressure flow rate at a fixed frequency. Typically the mass and/or stiffness of various components are altered to change the resonant frequency of the pump under the design operating conditions. If the pressure across the pump increases, the stiffness of the system is increased by back pressure across the diaphragm of the oscillating pump. The resonant frequency of the pump changes and the fixed frequency drive is not driving the pump at the optimum frequency. As a result, flow rate drops quickly and the capability of the pump to drive air at high pressure is limited. Accordingly, in order to provide increased flow rate at higher pressures requires either a sacrifice in flow rate at low pressures, or a pump of significantly greater size, when utilizing a fixed frequency oscillating pump. 
   For the foregoing reasons, there is a need for a vacuum assisted wound treatment system that is capable of automated pressure change over time. Additionally, there is a need for a more efficient vacuum assisted wound treatment system, that allows the patient more mobility, while reducing the risk of exudate spillage or pump contamination. 
   It is therefore an object of the present invention to provide a vacuum assisted wound treatment system that provides a means for increasing the stimulation of cellular growth by a variation of pressure over time. 
   A further object is to provide a system that is capable of extended operation in the absence of an alternating current power supply. 
   An additional object of the present invention is to provide a sanitary and cost effective means for sampling fluids drawn from the wound site without necessitating removal of the canister, or disturbing of the wound site. 
   Still another object of the present invention is to provide a vacuum assisted wound therapy device that can be secured to an object so as to reduce the likelihood of disturbance to the device, while still allowing convenient placement for its operation. 
   SUMMARY OF THE INVENTION 
   In accordance with the foregoing objects, the present invention generally comprises a porous pad for insertion substantially into a wound site and a wound drape for air-tight sealing enclosure of the pad at the wound site. A distal end of a tube is connected to the dressing in order to provide negative pressure at the wound site. A fluid sampling port is provided on the tube to allow for sampling of wound fluids being drawn through the tube from the wound site. A source of negative pressure is in communication with a proximal end of the tube. A collection canister is removably connected to the tube for collection of fluid removed from the wound during the application of negative pressure. A first filter is incorporated into an opening of the canister, and a second filter is positioned between the canister and the source of negative pressure. As the source of negative pressure may be an electric pump, supplied by alternating or direct current, a power management device, and its associated power management protocol, is incorporated to maximize battery life when the unit is being supplied by direct current. A clamping mechanism is utilized to secure the system to a stationary object, such as a bed rail, or pole, such as that used to suspend a container of intravenous fluid. 
   The pad, comprised of a foam having relatively few open cells in contact with the areas upon which cell growth is to be encouraged so as to avoid unwanted adhesions, but having sufficiently numerous open cells so that drainage and negative pressure therapy may continue unimpaired, is placed in fluid communication with a vacuum source for promotion of fluid drainage, as known in the art. The porous pad of the present invention may be comprised of polyvinyl alcohol foam. The fluid communication may be established by connecting a tube to a dressing, such as that described in International Application WO 99/13793, entitled “Surgical Drape and Suction Heads for Wound Treatment,” the disclosure of which is incorporated herein. 
   Upon placement of the pad, an airtight seal is formed over the wound site to prevent vacuum leakage. Such a seal may be provided by placing a drape over the wound, such that the drape adheres to the healthy skin surrounding the wound site, while maintaining an airtight seal over the wound itself. 
   A conduit or tube is placed in fluid communication with the foam pad, its distal end communicating with a fluid drainage canister which is in fluid communication with a vacuum source. A constant or intermitant negative pressure therapy is conducted as described in the prior art. Alternatively, the negative pressure is varied over time, so as to further stimulate cell growth, which in turn may shorten the healing process. The negative pressure induced on the wound adjusts to meet a varying target pressure, which oscillates between a target maximum and target minimum pressure. 
   Flow rate of a variable displacement pump, used in accordance with the present invention, is maximized over a pressure range by varying the drive frequency of the pump. The optimum drive frequency is continuously adjusted by a system that periodically or continuously monitors the pressure across the pump to determine the optimum drive frequency for that pressure. Pump performance is thereby improved over variable displacement pumps utilized in the prior art, without increasing pump size or weight. Similarly, pump performance of a typical variable displacement pump can be achieved with a smaller pump, which in turn reduces the size and weight of the overall system in order to improve ease of use and portability for the patient. An alternative negative pressure source, such as a fixed displacement pump, sometimes referred to as a positive displacement pump, may also be utilized. 
   The power management system is utilized to maximize battery life when the present invention is being supplied with electric power under direct current. The power management system comprises deactivation of a backlight to a display terminal, or touch screen liquid crystal display (LCD) control panel, after a predetermined interval. Battery life is further extended when the power management system prevents electric power from reaching an electric motor until the targeted power setting is actually large enough to activate the motor. In such an instance, the motor is utilized to provide negative pressure by driving an electric pump as known in the art. 
   The foregoing has outlined some of the more pertinent objects of the present invention. These objects should be construed to be merely illustrative of some of the more prominent features and applications of the invention. Many other beneficial results can be attained by applying the disclosed invention in a different manner or by modifying the invention as will be described. Accordingly, other objects and a fuller understanding of the invention may be had by referring to the following Detailed Description of the Invention, which includes the preferred embodiment 

   
     BRIEF DESCRIPTION OF THE DRAWINGS 
     These and other features and advantages of the invention will now be described with reference to the drawings of certain preferred embodiments, which are intended to illustrate and not to limit the invention, and wherein like reference numbers refer to like components, and in which: 
       FIG. 1  is a schematic block diagram of a tissue treatment system utilized in accordance with the present invention. 
       FIG. 2   a  is a perspective view of a fluid sampling port utilized in accordance with the present invention. 
       FIG. 2   b  is a perspective view of an alternative embodiment of a fluid sampling port utilized in accordance with the present invention. 
       FIG. 3   a  is a perspective view of the back portion of a pump housing utilized in accordance with the present invention. 
       FIG. 3   b  is a perspective view of the front portion of a pump housing utilized in accordance with the present invention. 
       FIGS. 4   a  and  4   b  are flow charts representing the preferred steps in the implementation of a power management system utilized in accordance with the present invention. 
       FIG. 5  is a flow chart illustrating the preferred steps in the implementation of pulse therapy utilized in accordance with the present invention. 
   

   DESCRIPTION 
   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  FIG. 1  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  FIGS. 2   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  FIG. 2   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  FIGS. 3   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  FIG. 4   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  FIG. 4   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  FIG. 3   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  FIG. 3   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  FIG. 1 , 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 FIG.  5 . 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.