US20070244415A1 - Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation - Google Patents
Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation Download PDFInfo
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- US20070244415A1 US20070244415A1 US11/811,373 US81137307A US2007244415A1 US 20070244415 A1 US20070244415 A1 US 20070244415A1 US 81137307 A US81137307 A US 81137307A US 2007244415 A1 US2007244415 A1 US 2007244415A1
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- acoustic energy
- transducer
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- audible acoustic
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H23/00—Percussion or vibration massage, e.g. using supersonic vibration; Suction-vibration massage; Massage with moving diaphragms
- A61H23/02—Percussion or vibration massage, e.g. using supersonic vibration; Suction-vibration massage; Massage with moving diaphragms with electric or magnetic drive
- A61H23/0218—Percussion or vibration massage, e.g. using supersonic vibration; Suction-vibration massage; Massage with moving diaphragms with electric or magnetic drive with alternating magnetic fields producing a translating or oscillating movement
- A61H23/0236—Percussion or vibration massage, e.g. using supersonic vibration; Suction-vibration massage; Massage with moving diaphragms with electric or magnetic drive with alternating magnetic fields producing a translating or oscillating movement using sonic waves, e.g. using loudspeakers
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N7/00—Ultrasound therapy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61H—PHYSICAL THERAPY APPARATUS, e.g. DEVICES FOR LOCATING OR STIMULATING REFLEX POINTS IN THE BODY; ARTIFICIAL RESPIRATION; MASSAGE; BATHING DEVICES FOR SPECIAL THERAPEUTIC OR HYGIENIC PURPOSES OR SPECIFIC PARTS OF THE BODY
- A61H2205/00—Devices for specific parts of the body
- A61H2205/08—Trunk
Definitions
- This invention relates to systems and methods for increasing blood perfusion and/or vasodilation.
- Vasodilation is a term that describes the increase in the internal diameter of a blood vessel that results from relaxation of smooth muscle within the wall of the vessel. Vasodilation can cause an increase in blood flow, as well as a corresponding decrease in systemic vascular resistance (i.e., reduced blood pressure). Tissue perfusion is a term that generally describes blood flow into the tissues.
- Vasodilation has been recognized to be beneficial in the treatment of myocardial infarction, strokes, and vascular diseases.
- Maintaining adequate tissue perfusion is recognized to be beneficial during any hypoperfused event, during any coronary syndrome including myocardial infarction, before, during, or after medical intervention (e.g., angioplasty, plastic and reconstructive surgery, maxillofacial surgery, vascular surgery, transplant surgery, or cardiac surgery); or before, during, or after dental procedures, or dermatological test patches and other skin challenges, or before, during, or after an exercise regime; or during wound healing.
- medical intervention e.g., angioplasty, plastic and reconstructive surgery, maxillofacial surgery, vascular surgery, transplant surgery, or cardiac surgery
- dental procedures e.g., or after dental procedures, or dermatological test patches and other skin challenges, or before, during, or after an exercise regime; or during wound healing.
- ultrasound energy upon enhanced. vasodilation and/or blood perfusion have been observed.
- the conventional use of ultrasound energy in medicine for either diagnostic or therapeutic purposes typically has involved the application of ultrasound energy at frequency ranges—e.g., about 2 MHz to 40 MHz for diagnostic purposes (ultrasound imaging), and about 1 MHz to 3 MHz (physiotherapy or diathermy devices)—and/or with attendant exposure times, that can induce thermal effects due to tissue absorption of ultrasound energy.
- These thermal mechanisms caused by tissue absorption of ultrasound energy can lead to substantial deep heating of tissue.
- the thermal mechanisms due to absorption of ultrasound energy in tissue can be intended and beneficial, or at least not detrimental.
- the invention provides systems and methods for applying audible acoustic energy to affect vasodilation and/or an increase in tissue perfusion.
- the desired physiologic effects can be achieved without substantial deep heating of tissue.
- FIG. 1 is a perspective view of a system for transcutaneously applying audible acoustic energy to affect vasodilation and/or increased blood perfusion.
- FIG. 2 is an enlarged exploded perspective view of an audible acoustic energy applicator that forms a part of the system shown in FIG. 1 .
- FIG. 3 is an enlarged assembled perspective view of the audible acoustic energy applicator shown in FIG. 2 .
- FIG. 4 is a side section view of the acoustic contact area of the audible acoustic energy applicator shown in FIG. 2 .
- FIG. 5 is a view of the applicator shown in FIG. 2 held by a stabilization assembly in a secure position overlaying the sternum of a patient, to transcutaneously direct acoustic energy, e.g., toward the heart.
- FIG. 6 is a side elevation view, with portions broken away and in section, of an acoustic stack that can be incorporated into the applicator shown in FIG. 2 .
- FIG. 7 is a side elevation view, with portions broken away and in section, of an acoustic stack that can be incorporated into the applicator shown in FIG. 2 .
- FIG. 8 a to 8 c graphically depict the technical features of a frequency tuning function that the system shown in FIG. 1 can incorporate.
- FIG. 9 graphically depicts the technical features of a power ramping function that the system shown in FIG. 1 can incorporate.
- FIG. 10 is a schematic view of a controller that the system shown in FIG. 1 can incorporate, which includes a frequency selection and tuning function, a power ramping function, and an output power control function.
- FIG. 11 is a diagrammatic view of a use register chip that forms a part of the use monitoring function shown in FIG. 10 .
- FIG. 12 is a diagrammatic flow chart showing the technical features of the use monitoring function shown in FIG. 10 .
- a system 10 will be described in connection with the therapeutic indication of providing vasodilation and/or increased tissue perfusion by the transcutaneous application of audible acoustic energy.
- audible acoustic energy means vibrational energy in a range of frequencies between about 20 Hz to no greater than 20 kHz.
- the audible acoustic energy is desirably indicated, e.g., for the treatment of myocardial infarction, strokes, and vascular diseases; and/or before, during, or after percutaneous or surgical intervention; and/or before, during, or after dental procedures; and/or before, during, or after dermatological test patches and other skin challenges; and/or before, during, or after prescribed exercise regimes; and/or during wound healing.
- the system 10 has application for use in diverse regions of the body, e.g., in the thoracic cavity, the abdomen, the arms, the legs, the neck, or the head.
- FIG. 1 schematically shows a compact, portable therapeutic system 10 that makes it possible to treat a person who needs or who is likely to need vasodilation and/or an increase in the flow rate to or perfusion of selected tissues.
- the system 10 includes durable and disposable equipment and materials necessary to treat the person at a designated treatment location. In use, the system 10 affects vasoldilation and/or increased tissue perfusion by transcutaneously applying audible acoustic energy.
- the system 10 includes at the treatment location an audible acoustic energy generating machine 16 .
- the system 10 also includes at the treatment location at least one audible acoustic energy applicator 18 , which is coupled to the machine 16 during use.
- the system 10 also includes an assembly 12 for use with the applicator 18 to stabilize the position of the applicator 18 on a patient for hands-free use.
- the applicator 18 is secured against movement on a person's thorax, overlaying the sternum, to direct acoustic energy toward the vasculature of the heart.
- the applicator can be sized and configured for placement on other regions of the body, such as the arms, legs, or head. The applicator can be secured to the patient as well.
- the location where treatment occurs can vary. It can be a traditional clinical setting, where support and assistance by one or more medically trained care givers are immediately available to the person, such as inside a hospital, e.g., in an emergency room, catheter lab, operating room, or critical care unit. However, due to the purposeful design of the system 10 , the location need not be confined to a traditional clinical setting.
- the location can comprise a mobile setting, such as an ambulance, helicopter, airplane, or like vehicle used to convey the person to a hospital or another clinical treatment center.
- the location can even comprise an everyday, public setting, such as on a cruise ship, or at a sports stadium or airport, or a private setting, such as in a person's home, where the effects of vasoconstriction and/or low tissue perfusion can arise.
- the system 10 can make it possible to initiate treatment of vasoconstriction and/or a reduced tissue perfusion incident in a non-clinical, even mobile location, outside a traditional medical setting.
- the system thereby makes effective use of the critical time period before the person enters a hospital or another traditional medical treatment center.
- FIG. 1 shows a representative embodiment of the audible acoustic energy generating machine 16 .
- the machine 16 can also be called an “audible acoustic energy generator.”
- the machine 16 is intended to be a durable item capable of long term, maintenance free use.
- the machine 16 can be variously sized and shaped to present a lightweight and portable unit, presenting a compact footprint suited for transport.
- the machine 16 can be sized and shaped to be mounted at bedside, or to be placed on a table top or otherwise occupy a relatively small surface area. This allows the machine 16 to travel with the patient within an ambulance, airplane, helicopter, or other transport vehicle where space is at a premium. This also makes possible the placement of the machine 16 in a non-obtrusive way within a private home setting, such as for the treatment of chronic angina.
- the machine 16 includes a chassis 22 , which, for example, can be made of molded plastic or metal or both.
- the chassis 22 houses a module 24 for generating electric signals.
- the signals are conveyed to the applicator 18 by an interconnect 30 to be transformed into acoustic energy.
- a controller 26 also housed within the chassis 22 (but which could be external of the chassis 22 , if desired), is coupled to the module 24 to govern the operation of the module 24 . Further desirable technical features of the controller 26 will be described later.
- the machine 16 also preferably includes an operator interface 28 .
- the operator uses the interface 28 to input information to the controller 26 to affect the operating mode of the module 24 .
- the controller 26 also outputs status information for viewing by the operator.
- the interface 28 can provide a visual readout, printer output, or an electronic copy of selected information regarding the treatment.
- the interface 28 is shown as being carried on the chassis 22 , but it could be located external of the chassis 22 as well.
- the machine 16 includes a power cord 14 for coupling to a conventional electrical outlet, to provide operating power to the machine 16 .
- the machine 16 can also include a battery module (not shown) housed within the chassis 22 , which enables use of the machine 16 in the absence or interruption of electrical service.
- the battery module can comprise rechargeable batteries, which can be built in the chassis 22 or, alternatively, be removed from the chassis 22 for recharge.
- the battery module (or the machine 16 itself) can include a built-in or removable battery recharger.
- the battery module can comprise disposable batteries, which can be removed for replacement.
- Power for the machine 16 can also be supplied by an external battery and/or line power module outside the chassis 22 .
- the battery and/or line power module is releasably coupled at time of use to the components within the chassis 22 , e.g., via a power distribution module within the chassis 22 .
- the provision of battery power for the machine 16 frees the machine 16 from the confines surrounding use of conventional ultrasound equipment, caused by their dependency upon electrical service.
- This feature makes it possible for the machine 16 to provide a treatment modality that continuously “follows the patient,” as the patient is being transported to or inside a transport vehicle, or as the patient is being shuttled between different locations within a treatment facility, e.g., from the emergency room to a catheterization lab or holding area within or outside the emergency room.
- the chassis 22 measures about 12 inches ⁇ about 8 inches ⁇ about 8 inches and weighs about 9 pounds.
- the applicator 18 can also be called the “patient interface.”
- the applicator 18 comprises the link between the machine 16 and the treatment site within the thoracic cavity of the person undergoing treatment.
- the applicator 18 converts electrical signals from the machine 16 to acoustic energy, and further directs the acoustic energy to the targeted treatment site.
- the applicator 18 is intended to be a disposable item. At least one applicator 18 is coupled to the machine 16 via the interconnect 30 at the beginning a treatment session. The applicator 18 is preferably decoupled from the interconnect 30 (as FIG. 1 shows) and discarded upon the completing the treatment session. However, if desired, the applicator 18 can be designed to accommodate more than a single use.
- the audible acoustic energy applicator 18 includes a shaped metal or plastic body 38 ergonomically sized to be comfortably grasped and manipulated in one hand.
- the body 38 houses and supports at least one audible acoustic energy transducer 40 (see FIG. 3 ).
- the audible acoustic energy transducer 40 comprises an acoustic stack 20 .
- the acoustic stack 20 comprises a front mass piece 32 , a back mass piece 34 , and one or more piezoelectric elements 36 , which are bolted together.
- the back mass piece 34 comprises an annular ring of material having relatively high acoustic impedance, e.g., steel or stainless steel. “Acoustic impedance” is defined as the product. of the density of the material and the speed of sound.
- the front mass piece 32 comprises a cone-shaped piece of material having relatively low acoustic impedance, e.g., aluminum or magnesium.
- the piezoelectric elements 36 are annular rings made of piezoelectric material, e.g., PZT.
- An internally threaded hole or the like receives a bolt 42 that mechanically biases the acoustic stack 20 .
- a bolt 42 that can be used for this purpose is shown in U.S. Pat. No. 2,930,912.
- the bolt 42 can extend entirely through the front mass piece 32 or, the bolt 42 can extend through only a portion of the front mass piece 32 (see FIG. 7 ).
- the acoustic stack 20 ′ of a transducer 40 ′ can comprise a single piezoelectric element 36 ′ sandwiched between front and back mass pieces 32 ′ and 34 ′.
- the back mass piece 34 ′ is electrically insulated from the front mass piece 32 ′ by, e.g., an insulating sleeve and washer 44 .
- the piezoelectric element(s) 36 / 36 ′ have electrodes 46 (see FIG. 2 ) on major positive and negative flat surfaces.
- the electrodes 46 electrically connect the acoustic stack 20 of the transducer 40 to the electrical signal generating module 24 of the machine 16 .
- the piezoelectric elements 36 / 36 ′ convert the electrical energy into mechanical (i.e., acoustic) energy in the form of mechanical vibration.
- the mechanical vibration created by the transducer 40 / 40 ′ is coupled to a patient through a transducer bladder 48 , which rests on a skin surface.
- the bladder 48 defines a bladder chamber 50 (see FIG. 4 ) between it and the front mass piece 32 .
- the bladder chamber 50 spaces the front mass piece 32 a set distance from the patient's skin.
- the bladder chamber 50 accommodates a volume of an acoustic coupling media liquid, e.g., liquid, gel, oil, or polymer, that is conductive to acoustic energy, to further cushion the contact between the applicator 18 and the skin.
- the presence of the acoustic coupling media also makes the acoustic contact area of the bladder 48 more conforming to the local skin topography.
- an acoustic coupling medium is also applied between the bladder 48 and the skin surface.
- the coupling medium can comprise, e.g., a gel material (such as AQUASONIC® 100, by Parker Laboratories, Inc., Fairfield, N.J.).
- the external material can possess sticky or tacky properties, to further enhance the securement of the applicator 18 to the skin.
- the bladder 48 and bladder chamber 50 together form an integrated part of the applicator 18 .
- the bladder 48 and bladder chamber 50 can be formed by a separate molded component, e.g., a gel or liquid filled pad, which is supplied separately.
- a molded gel filled pad adaptable to this purpose is the AQUAFLEX® Ultrasound Gel Pad sold by Parker Laboratories (Fairfield, N.J.).
- the front mass piece 32 of the acoustic stack 20 measures about 2 inches in diameter, whereas the acoustic contact area formed by the bladder 48 measures about 5 inches in diameter.
- An applicator 18 that presents an acoustic contact area of larger diameter than the front mass piece 32 of the transducer 40 provides a propagation path for the diverging acoustic beam. Also, a large contact area provides additional stability (with the assembly 12 ) in hands-free use.
- the applicator 18 measures about 5 inches in diameter about the bladder 48 , about 5 inches in height, and weighs about one pound.
- the diameter of the front mass piece 32 is sized to deliver acoustic energy in a desired range of fundamental frequencies to substantially the entire targeted region.
- the fundamental frequencies lay in a frequency range of about 20 Hz to about 20 kHz, and most desirably, in a range of between 15 kHz and 20 kHz.
- the applicator 18 should be sized to percutaneously transmit the energy in a diverging beam, which substantially covers the entire heart and coronary circulation.
- the applicator 18 may comprise a single transducer or an array of transducers that together form an acoustic contact area.
- Normal hearts vary significantly in size and distance from skin between men and women, as well as among individuals regardless of sex.
- the size of a normal heart ranges between 8 to 11 cm in diameter and 6 to 9 cm in depth, and the weight ranges between 300 to 350 grams.
- the distance between the skin and the anterior surface of the heart (which will be called the “subcutaneous depth” of the heart) ranges between 4 to 9 cm.
- the size of a normal heart ranges between 7 to 9 cm in diameter and 5 to 8 cm in depth, and the weight ranges between 250 to 300 grams.
- the subcutaneous depth of the heart ranges between 3 to 7 cm.
- the degree of divergence or “directivity” of the acoustic beam transmitted percutaneously through the acoustic contact area is a function of the wavelength of the energy being transmitted. Generally speaking, as the wavelength increases, the beam divergence becomes larger (given a fixed aperture size). If the beam divergence at the subcutaneous depth of the heart is less than beam area of the heart, the audible acoustic energy will not be delivered to substantially the whole heart. Therefore, the beam divergence should desirably be essentially equal to or greater than the targeted beam area at the subcutaneous depth of the heart.
- the beam divergence can be expressed in terms of an aperture size measured in wavelengths.
- the term “effective diameter” is intended to encompass a geometry that is “round,” as well as a geometry that is not “round”, e.g., being elliptical or rectilinear, but which possesses a surface area in contact with skin that can be equated to an equivalent round geometry of a given effective diameter.
- front mass pieces 32 characterized by aperture sizes laying within a range of 0.5 to 5 wavelengths, and preferably less than 2 wavelengths, possess the requisite degree of beam divergence to transcutaneously deliver audible acoustic energy from a position on the thorax, and preferably on or near the sternum, to substantially an entire normal heart of a man or a woman.
- the transducer face 46 can be suitably sized for other applications within the thoracic cavity or elsewhere in the body.
- the front mass piece 32 can be sized to delivery energy to beyond the heart and the coronary circulation, to affect the pulmonary circulation.
- An O-ring 52 (see FIG. 4 ) is captured within a groove 54 in the body 38 of the applicator 18 and a groove 84 on the front mass piece 32 of the transducer 40 .
- the O-ring 52 seals the bladder chamber 50 and prevents liquid in the chamber 50 from contacting the sides of the front mass piece 32 .
- FIG. 4 shows, only the radiating surface of the front mass piece 32 is in contact with the acoustic coupling medium within the chamber 50 .
- the material of the O-ring 52 is selected to possess elasticity sufficient to allow the acoustic stack 20 of the transducer 40 to vibrate freely in a piston-like fashion within the transducer body 38 . Still, the material of the O-ring 52 is selected to be sturdy enough to prevent the acoustic stack 20 , while vibrating, from popping out of the grooves 54 and 84 .
- the O-ring 52 is formed from nitrile rubber (Buna-N) having a hardness of about 30 Shore A to about 100 Shore A.
- the O-ring 52 has a hardness of about 65 Shore A to about 75 Shore A.
- the bladder 48 is stretched across the face of the bladder chamber 50 and is preferably also locked in place with another O-ring 56 (see FIG. 4 ).
- a membrane ring may also be used to prevent the O-ring 56 from popping loose.
- the membrane ring desirably has a layer or layers of soft material (e.g., foam) for contacting the skin.
- the bladder 48 desirably presents a flexible, essentially flat radiating surface contour where it contacts the individual's skin (see FIG. 4 ), or a flexible, outwardly bowed or convex radiating surface contour (i.e., curved away from the front mass piece) where it contacts with or conducts acoustic energy to the individual's skin.
- a flexible flat or convex surface contour can “mold” evenly to the individual's skin topography, to thereby mediate against the collection and concentration of air bubbles in the contact area where skin contact occurs.
- the interior of the bladder chamber 50 can include a recessed well region 58 surrounding the front mass piece 32 .
- the well region 58 is located at a higher gravity position than the plane of the front mass piece 32 . Air bubbles that may form in fluid located in the bladder chamber 50 are led by gravity to collect in the well region 58 away from the acoustic energy beam path.
- the front mass piece 32 desirably possesses either a flat radiating surface (as FIG. 4 shows) or a convex radiating surface (as FIG. 7 shows).
- the convex radiation surface directs air bubbles off the radiating surface.
- the radiating surface of the front mass piece may also be coated with a hydrophilic material 60 (see FIG. 4 ) to prevent air bubbles from sticking.
- the transducer 40 may also include a reflux valve/liquid inlet port 62 .
- the interconnect 30 carries a distal connector 80 (see FIG. 2 ), designed to easily plug into a mating outlet in the applicator 18 .
- a proximal connector 82 on the interconnect 30 likewise easily plugs into a mating outlet on the chassis 22 (see FIG. 1 ) , which is itself coupled to the controller 26 .
- the applicator 18 can be quickly connected to the machine 16 at time of use, and likewise quickly disconnected for discard once the treatment session is over.
- Other quick-connect coupling mechanisms can be used.
- the interconnect 30 can be hard wired as an integrated component to the applicator 18 with a proximal quick-connector to plug into the chassis 22 , or, vice versa, the interconnect 30 can be hard wired as an integrated component to the chassis 22 with a distal quick-connector to plug into the applicator 18 .
- the stabilization assembly 12 allows the operator to temporarily but securely mount the applicator 18 against an exterior skin surface for use.
- the attachment assembly 54 is fashioned to secure the applicator 18 on the person's thorax, overlaying the sternum or breastbone, as FIG. 5 shows.
- the assembly 12 can be variously constructed. As shown in FIG. 5 , the assembly 12 comprises straps 90 that pass through brackets 92 carried by the applicator 18 . The straps 90 encircle the patient's neck and abdomen.
- the stabilization assembly 12 also preferably makes the task of securing and removing the applicator 18 on the patient simple and intuitive.
- the stabilization assembly 12 makes it possible to secure the applicator 18 quickly and accurately in position on the patient in cramped quarters or while the person (and the system 10 itself) is in transit.
- the system 10 applies audible acoustic energy to achieve vasodilation and/or an increase tissue perfusion without causing substantial deep tissue heating.
- the system 10 incorporates selection and tuning of an output frequency.
- the system 10 can also incorporate other features such as power ramping, output power control, and the application of audible acoustic energy at the selected frequency in pulses.
- the controller 26 desirably operates a given transducer 40 at a fundamental frequency in the range of about 20 kHz or less.
- the fundamental frequencies lay in a frequency range of about 20 Hz to 20 kHz, and desirably within a range of 15 kHz to 20 kHz.
- the applicator 18 can include multiple transducers 40 (or multiple applicators 18 can be employed simultaneously for the same effect), which can be individually conditioned by the controller 26 for operation.
- One or more transducers 40 within an array of transducers 40 can be operated, e.g., at different fundamental frequencies.
- one or more transducers 40 can be operated at about 15 kHz, while another one or more transducers 40 can be operated at about 20 kHz.
- More than two different fundamental frequencies can be used, e.g., about 15 kHz, about 18 kHz, and about 20 kHz.
- the controller 26 can trigger the fundamental frequency output according to time or a physiological event (such as ECG or respiration).
- the controller 26 desirably includes a tuning function 64 .
- the tuning function 64 selects an optimal frequency at the outset of each treatment session.
- the tuning function sweeps the output frequency within a predetermined range of frequencies (f-start to f-stop).
- the frequency sweep can be and desirably is done at an output power level that is lower than the output power level of treatment (see FIG. 9 ).
- the frequency sweep can also be done in either a pulsed or a continuous mode, or in a combination of these two modes.
- An optimal frequency of operation is selected based upon one or more parameters sensed during the sweeping operation.
- the frequency sweep can progress from a lower frequency (f-start) to a higher frequency (f-stop), or vice versa.
- the sweep can proceed on a linear basis (as FIG. 8A also shows), or it can proceed on a non-linear basis, e.g., logarithmically or exponentially or based upon another mathematical function.
- the range of the actual frequency sweep may be different from the range that is used to determine the frequency of operation. For instance, the frequency span used for the determination of the frequency of operation may be smaller than the range of the actual sweep range.
- the tuning function 64 adjusts the output voltage and/or current to maintain a constant output power level (p-constant).
- the function 64 also senses changes in transducer impedance (see FIG. 8B )—Z-min to Z-max—throughout the frequency sweep.
- the tuning function 64 selects as the frequency of operation the frequency (f-tune) where, during the sweep, the minimum magnitude of transducer impedance (Z-min) is sensed. Typically, this is about the same as the frequency of maximum output current (I), which in turn, is about the same as the frequency of minimum output voltage (V).
- the tuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum of real part (R) of transducer impedance (Z) occurs, where:
- ⁇ ( R 2 +X 2 )
- R is the real part
- X is the imaginary part
- the tuning function 64 can maintain a constant output voltage.
- the tuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum output power occurs.
- the tuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum output current occurs.
- the tuning function 64 desirably operates at an output power level lower than the power level of treatment. In this arrangement, once the operating frequency has been selected, the output power level needs to be increased to the predetermined output level to have the desired therapeutic effect.
- the controller 26 desirably includes a ramping function 66 .
- the ramping function 66 causes a gradual ramp up of the output power level at which the tuning function 64 is conducted (e.g., 5 W) to the power level at which treatment occurs (e.g., 25 W).
- the gradual ramp up decreases the possibility of unwanted patient reaction to the acoustic exposure. Further, a gradual ramp up is likely to be more comfortable to the patient than the sudden onset of the full output power.
- the ramping function 66 increases power at a rate of about 0.01 W/s to about 10 W/s.
- a particularly desired ramping rate is between about 0.1 W/s to about 5 W/s.
- the ramping function 66 desirably causes the ramp up in a linear fashion (as FIG. 9 shows).
- the ramping function can employ non-linear ramping schemes, e.g., logarithmic or according to another mathematical function.
- the controller 26 can operate a given transducer 40 at a prescribed power level, which can remain fixed or can be varied during the treatment session.
- the controller 26 can also operate one or more transducers 40 within an array of transducers 40 (or when using multiple applicators 18 ) at different power levels, which can remain fixed or themselves vary over time.
- the parameters affecting power output take into account the output of the signal generator module; the physical dimensions and construction of the applicator; and the physiology of the tissue region to which acoustic energy is being applied.
- the parameters affecting power output can take into account the output of the signal generator module 24 ; the physical dimensions and construction of the applicator 18 ; and the physiology of the tissue region to which acoustic energy is being applied.
- these parameters include the total output power (P Total ) (expressed in watts—W) provided to the transducer 40 by the signal generator module 24 ; the intensity of the power (expressed in watts per square centimeter—W/cm 2 ) in the effective radiating area of the applicator 18 , which takes into account the total power P Total , and the area of the bladder 48 ; and the peak rarefactional acoustic pressure (P peak(Neg) ) (expressed in Pascals—Pa) that the tissue experiences, which takes into consideration that the physiological tolerance of tissue to rarefactional pressure conditions is much less than its tolerance to compressional pressure conditions.
- P Peak(Neg) can be derived as a known function of W/cm 2 .
- the applicator 18 can be sized to provide an intensity equal to or less than 25 W/cm 2 at a maximum total power output of equal to or less than 200 W (most preferably 15 W. P Total 150 W) operating at a fundamental frequency of less than or equal to 20 kHz.
- Audible acoustic energy within the range of fundamental frequencies specified passes through bone, while also providing selectively different mechanical effects (depending upon the frequency), and without substantial deep tissue heating effects, as previously described. Power supplied within the total power output range specified meets the size, capacity, and cost requirements of battery power, to make a transportable, “follow the patient” treatment modality possible, as already described.
- Audible acoustic energy supplied within the power density range specified keeps peak rarefactional acoustic pressure within physiologically tolerable levels.
- the applicator 18 meeting these characteristics can therefore be beneficially used in conjunction with the transportable audible energy generator machine 16 , as described.
- the transducer impedance may vary due to a number of reasons, e.g., transducer heating, changes in acoustic coupling between the transducer and patient, and/or changes in transducer bladder fill volume, for instance, due to degassing.
- the controller 26 includes an output power control function 68 .
- the output power control function 68 holds the output power constant, despite changes in transducer impedance within a predetermined range. If the transducer falls out of the predetermined range, for instance, due to an open or short circuit, the controller 26 shuts down the generator audible acoustic energy module 24 and desirably sounds an alarm.
- the output power control function 68 Governed by the output power control function 68 , as the transducer impedance increases, the output voltage is increased to hold the power output constant. Should the output voltage reach a preset maximum allowable value, the output power will decrease, provided the transducer impedance remains within its predetermined range. As the transducer impedance subsequently drops, the output power will recover, and the full output power level will be reached again.
- the output power control function 68 Governed by the output power control function 68 , as the transducer impedance decreases, the output current is increased to hold the power output constant. Should the output current reach a preset maximum allowable value, the output power will decrease until the impedance increases again, and will allow full output power.
- the output power control function 68 can vary the frequency of operation slightly upward or downward to maintain the full output power level within the allowable current and voltage limits.
- the application of audible acoustic energy in a pulsed power mode serves, in conjunction with the selection of the fundamental output frequency, to reduce deep heating tissue effects. This is because, at a given frequency, a high acoustic intensity, or high acoustic power, results in more deep heating of tissue than a low intensity, or power. At the same peak acoustic intensity, the pulse mode application of acoustic energy results in less deep heating of tissue than continuous mode because tissue is cooled off in between the pulses.
- audible acoustic energy is applied at a desired fundamental frequency or within a desired range of fundamental frequencies at the prescribed power level or range of power levels (as described above, to achieve the desired physiological effect) in a prescribed duty cycle (DC) (or range of duty cycles) and a prescribed pulse repetition frequency (PRF) (or range of pulse repetition frequencies).
- DC duty cycle
- PRF pulse repetition frequency
- the pulse repetition frequency (PRF) is between about 20 Hz to about 50 Hz (i.e., between about 20 pulses a second to about 50 pulses a second).
- the duty cycle (DC) is equal to the pulse duration (PD) divided by one over the pulse repetition frequency (PRF).
- the pulse duration (PD) is the amount of time for one pulse.
- the pulse repetition frequency (PRF) represents the amount of time from the beginning of one pulse to the beginning of the next pulse. For example, given a pulse repetition frequency (PRF) of 30 Hz (30 pulses per second) and a duty cycle of 25% yields a pulse duration (PD) of approximately 8 ms pulse followed by a 25 ms off period 30 times per second.
- a duty cycle of about 50% or less meets the desired physiological objectives with less incidence of localized conductive heating effects compared to a continuous application of the same fundamental frequency and power levels over a comparable period of time.
- the duty cycle desirably lays in a range of between about 1% and about 35%.
- the controller 26 desirably includes a use monitoring function 70 (see FIG. 10 ) that monitors incidence of use of a given transducer 40 .
- the transducer 40 carries a use register 72 (see FIG. 4 ).
- the use register 72 is configured to record information before, during, and after a given treatment session.
- the use register 72 can comprise a solid state micro-chip, ROM, EEROM, EPROM, or non volatile RAM (NVRAM) carried by the transducer 40 .
- the use register 72 is initially formatted and programmed by the manufacturer of the system to include memory fields.
- the memory fields of the use register are of two general types: Write Many Memory Fields 74 and Write-Once 10 Memory Fields 76 .
- the Write Many Memory Fields 74 record information that can be changed during use of the transducer 40 .
- the Write-Once Memory Fields 76 record information that, once recorded, cannot be altered.
- the specific information recorded by the Memory 15 Fields 74 and 76 can vary.
- the following table exemplifies typical types of information that can be recorded in the Write Many Memory Fields 74 .
- Field Size Name Description Location (Byte) Treatment If a transducer has been used for a 0 1 Complete prescribed maximum treatment time (e.g., 60 minutes), the treatment complete flag is set to 1 otherwise it is zero. Prescribed This is the allowable usage time of 1-2 2 Maximum the transducer. This is set by the Treatment manufacturer and determines at what Time point the Treatment Complete flag (Minutes) is set to 1. Elapsed Initialized to zero. This area is 3-4 2 Usage Time then incremented every minute that (Minutes) the system is transmitting acoustic energy.
- Transducer This is an area that could be used 5-6 2 Frequency to prescribe the operational frequency of the transducer, rather than tuning the transducer to an optimal frequency, as above described. In the latter instance, this area shows the tuned frequency once the transducer has been tuned. Average The system reads and accumulates 7-8 2 Power the delivered power throughout the (Watts) procedure. Every minute, the average power number is updated in this area from the system, at the same time the Elapsed Usage Time is updated. when the Usage time clock is updated.
- the on/off cycles of acoustic energy transmission could affect the accuracy of the recorded power levels because of the variance of the power levels due to ramping function 66 . For this reason it may be advantageous to also record the number of on/off cycles of acoustic energy transmission. This will help explain any discrepancies in the average power reading. It might also allow the identification of procedural problems with system use.
- Each use register 72 can be assigned a unique serial number that could be used to track transducers in the field. This number can be read by the use monitoring function 70 if desired.
- the following table exemplifies typical types of information that can be recorded in the Write-Once Memory Fields 76 .
- Field Size Name Description Location (Byte) Treatment If a transducer has been used for 0 1 Complete a prescribed maximum treatment time (e.g., 60 minutes), the treatment complete flag is set to 1 otherwise it is zero. Prescribed This is the allowable usage time 1-2 2 Maximum of the transducer. This is set by Treatment the manufacturer and determines at Time what point the Treatment Complete (Minutes) flag is set to 1. Elapsed Initialized to zero. This area 3-4 2 Usage Time is then incremented every minute (Minutes) that the system is transmitting acoustic energy. This area keeps track of the amount of time that the transducer has been used.
- Transducer This is an area that could be 5-6 2 Frequency used to prescribe the operational frequency of the transducer, rather than tuning the transducer to an optimal frequency, as above described. In the latter instance, this area shows the tuned frequency once the transducer has been tuned.
- Average The system reads and accumulates 7-8 2 Power the delivered power throughout the (Watts) procedure. Every minute, the average power number is updated in this area from the system, at the same time the Elapsed Usage Time is updated. When the Usage time clock is updated. This means that the average power reading could be off by a maximum of 59 seconds if the treatment is stopped before the Treatment Complete flag is set.
- This average power can be used as a check to make sure that the system was running at full power during the procedure.
- Applicator Use Register CRC This desirably 9-10 2 CRC uses the same CRC algorithm used to protect the controller ROM. Copyright Desirably, the name of the 11-23 11 Notice manufacturer is recorded in this area. Other information can be recorded here as well.
- the on/off cycles of acoustic energy transmission could affect the accuracy of the recorded power levels because of the variance of the power levels due to ramping function 66 . For this reason it may be advantageous to also record the number of on/off cycles of acoustic energy transmission. This will help explain any discrepancies in the average power reading. It might also allow the identification of procedural problems with system use.
- Each use register 72 can be assigned a unique serial number that could be used to track transducers in the field. This number can be read by the use monitoring function 70 if desired.
- the following table exemplifies typical types of information that can be recorded in the Write-Once Memory Fields 76 .
- Size Field Name Description (Bytes) Start Date Once the system has tuned the transducer Time and started to transmit acoustic energy, the current date and time are written to this area. This area is then locked, which prevents the data from ever-being changed. Tuned The tuned frequency is written to this Frequency location when the Start Date and Time is set. This prevents this information from being written over on subsequent tunes (if necessary).
- FIG. 12 shows, when a transducer 40 is first coupled to the machine 16 , and prior to enabling the conveyance of audible acoustic energy to the transducer 40 , the use monitoring function 70 prompts the use register 72 to output resident information recorded in the memory fields.
- the use monitoring function 70 compares the contents of the Copyright Notice field to a prescribed content.
- the prescribed content includes information contained in the Copyright Notice field of the Write Many Memory Fields 74 .
- the prescribed content therefore includes the name of the manufacturer, or other indicia uniquely associated with the manufacture. If the prescribed content is missing, the use monitoring function 70 does not enable use of the transducer 40 , regardless of the contents of any other memory field. The transducer 40 is deemed “invalid.” In this way, a manufacturer can assure that only transducers meeting its design and quality control standards are operated in association with the machine 16 .
- the use monitoring function 70 compares the digital value residing in the Treatment Complete field of the Write Many Memory Fields 74 to a set value that corresponds to a period of no prior use or a prior use less than the Prescribed Maximum Treatment Time—i.e., in the illustrated embodiment, a zero value.
- a different value i.e., a 1 value
- the use monitoring function 70 does not enable use of the transducer 40 .
- the transducer 40 is deemed “invalid.”
- the use monitoring function 70 compares the date and time data residing in the Write-Once Start Date and Time field to the current date and time established by a Real Time Clock. If the Start Date and Time is more than a prescribed time before the Real Time (e.g., 4 hours), the controller does not enable use of the transducer 40 . The transducer 40 is deemed “invalid.”
- the use monitoring function 70 deems the transducer 40 to be “valid” (providing the preceding other criteria have been met).
- the use monitoring function 70 reports a valid transducer to the controller 26 , which initiates the tuning function 64 . If the Start Date and Time field is empty, once the tuning function 64 is completed, the controller prompts the use monitoring function 70 to records the current date and time in the Start Date and Time Field, as well as the selected operating frequency in the Tuned Frequency field. The controller 26 then proceeds to execute the ramping function 66 and, then, execute the prescribed treatment protocol.
- the controller 26 immediately proceeds with the ramping function 66 and, then, execute the treatment protocol.
- the use monitoring function 70 periodically updates the Elapsed Usage Time field and Average Power field (along with other Many Write Memory Fields). Once the Treatment Complete flag is set to a 1 value (indicating use of the transducer beyond the Prescribed Maximum Treatment Time), the use monitoring function 70 interrupts the supply of energy to the transducer. The transducer 40 is deemed “invalid” for subsequent use.
- the use monitoring function 70 can also generate an output that results in a visual or audible alarm, informing the operator that the transducer 40 cannot be used.
- the information recorded in the use register 72 can also be outputted to monitor use and performance of a given transducer 40 .
- Other sensors can be used, e.g., a temperature sensor 78 carried on the front mass piece 32 (see FIG. 4 ), in association with the use register.
- the use register 72 allows specific pieces of information to be recorded before, during and after a treatment is complete. Information contained in the use register 72 is checked before allowing use of a given transducer 40 .
- the use register 72 ensures that only a transducer 40 having the desired design and performance criteria imparted by the manufacturer can be used.
- the use register 72 can be used to “lock out” a transducer 40 and prevent it from being used in the future. The only way the transducer 40 could be reused is to replace the use register 72 itself.
- copying the architecture of the use register 72 (including the contents of the Copyright Message field required for validation) itself constitutes a violation of the manufacturer's copyright in a direct and inescapable way.
- the system 10 can be further include at the treatment location a delivery system for introducing a therapeutic agent in conjunction with the use of the applicator 18 and machine 16 .
- a delivery system for introducing a therapeutic agent in conjunction with the use of the applicator 18 and machine 16 .
- the effect of vasodilation and/or increased tissue perfusion caused by the application of audible acoustic energy can also be enhanced by the therapeutic effect of the agent, or vice versa.
- the therapeutic agent can comprise a thrombolytic agent.
- the thrombolytic agent is introduced into a thrombosis site, prior to, in conjunction with, or after the application of audible acoustic energy.
- the interaction between the applied audible acoustic energy and the thrombolytic agent is observed to assist in the breakdown or dissolution of the trombi, compared with the use of the thrombolytic agent in the absence of audible acoustic energy.
- This phenomenon is discussed, e.g., in Carter U.S. Pat. No. 5,509,896; Siegel et al U.S. Pat. No. 5,695,460; and Lauer et al U.S. Pat. No. 5,399,158, which are each incorporated herein by reference.
- thrombolysis is affected by use of audible acoustic energy in conjunction with a thrombolytic agent
- the application of acoustic energy has been shown to cause reversible changes to the fibrin structure within the thrombus, increased fluid dispersion into the thrombus, and facilitated enzyme kinetics. These mechanical effects beneficially enhance the rate of dissolution of thrombi.
- cavitational disruption, acoustic radiation pressure and streaming effects can also assist in the breakdown and dissolution of thrombi.
- the type of thrombolytic agent used can vary.
- the thrombolytic agent can comprise a drug known to have a thrombolytic effect, such as t-PA, TNKase, or RETAVASE.
- the agent can comprise an anticoagulant, such as heparin; or an antiplatelet drug, such as GP IIb IIIa inhibitor; or a fibrinolytic drug; or a non-prescription agent having a known beneficial effect, such as aspirin.
- the thrombolytic agent can comprise microbubbles, which can be acoustically activated; or microparticles, which contain albumin.
- the syndrome being treated can also vary, according to the region of the body.
- the thrombolytic syndrome can comprise acute myocardial infarction, or acute coronary syndrome.
- the syndrome can alternatively comprise suspect myocardial ischemia, blumetal angina, chronic angina, or pulmonary embolism.
- the thrombolytic agent is typically administered by a delivery system intravenously prior to or during the application of acoustic energy.
- the dosage of the thrombolytic agent is determined by the physician according to established treatment protocols.
- thrombolytic agent when acoustic energy is also applied. It also may be possible to use a less expensive thrombolytic agent or a less potent thrombolytic agent when acoustic energy is applied.
- the ability to reduce the dosage of thrombolytic agent, or to otherwise reduce the expense of thrombolytic agent, or to reduce the potency of thrombolytic agent, when audible acoustic energy is also applied, can lead to additional benefits, such as decreased complication rate, an increased patient population eligible for the treatment, and increased locations where the treatment can be administered (i.e., outside hospitals and critical care settings, as well as in private, in-home settings).
- Treatment using audible acoustic energy alone can simulate additional capillary or microcirculatory activity, resulting in an arteriogenesis/angiogenesis effect.
- This treatment can be used as an adjunct to treatment using angiogenic agents released in the coronary circulation to promote new arterial or venous growth in ischemic cardiac tissue or elsewhere in the body.
- the therapeutic agent can comprise an angiogenic agent, e.g., Monocyte Chemoattractant Protein-1, or Granulocyte-Macrophage Colony-Stimulating-Factor.
- angiogenic effects of these agents can be enhanced by shear-related phenomena associated with increased blood flow through the affected area.
- Increased blood perfusion in the heart caused by the application of audible acoustic energy can induce these shear-related phenomena in the presence of the angiogenic agents, and thereby lead to increased arterial-genesis and/or vascular-genesis in ischematic heart tissue.
- the system 10 can be used to carry out other therapeutic treatment objectives, as well.
- the system 10 can be used to carry out cardiac rehabilitation.
- the repeated application of audible acoustic energy over an extended treatment period can exercise and strengthen heart muscle weakened by disease or damage.
- treatment using audible acoustic energy can facilitate an improvement in heart wall motion or function.
- the system 10 may also be used in association with other diagnostic or therapeutic modalities to achieve regional systemic therapy.
- a first selected treatment modality can be applied to the body to achieve a desired systemic effect (for example, the restriction of blood flow).
- a second selected treatment modality which comprises the audible acoustic energy delivery system 10 previously described, can also be applied before, during, or after the first treatment modality, at least for a period of time, to transcutaneously apply acoustic energy to a selected localized region of the body (e.g., the thoracic cavity) to achieve a different, and perhaps opposite, localized system result, e.g., increased tissue perfusion.
- an individual who has received a drug that systemically decreases blood flow or blood pressure may experience a need for increased blood perfusion to the heart, e.g., upon experiencing a heart attack.
- the audible acoustic energy delivery system 10 can be used to locally apply audible acoustic energy to the thoracic cavity, to thereby locally increase blood perfusion to and in the heart, while systematic blood perfusion remains otherwise lowered outside the region of the heart due to the presence of the drug in the circulatory system of the individual.
- a chemotherapy drug may be systemically or locally delivered (by injection or by catheter) to an individual.
- the audible acoustic energy delivery system 10 can be used to locally supply audible acoustic energy to the targeted region, where the tumor is, to locally increase perfusion or uptake of the drug.
- the purposeful design of the durable and disposable equipment of the system 10 makes it possible to carry out these therapeutic protocols outside a traditional medical setting, such as in a person's home.
Abstract
Systems and methods apply audible acoustic energy to cause vasodilation and/or to increase tissue perfusion.
Description
- This application is a divisional of co-pending patent application Ser. No. 10/359,040 filed 5 Feb. 2003, which claims the benefit of Ser. No. 10/202,447, filed Jul. 24, 2002, entitled “Systems and Methods for Monitoring and Enabling Use of a Medical Instrument.” This application also claims the benefit of Ser. No. 09/935,908, filed Aug. 23, 2001, entitled “Systems and Methods for Applying Ultrasonic Energy to the Thoracic Cavity.” This application also claims the benefit of Ser. No. 09/645,662, filed Aug. 24, 2000, entitled “Systems and Methods for Enhancing Blood Perfusion Using Ultrasound Energy.”
- This invention relates to systems and methods for increasing blood perfusion and/or vasodilation.
- Vasodilation is a term that describes the increase in the internal diameter of a blood vessel that results from relaxation of smooth muscle within the wall of the vessel. Vasodilation can cause an increase in blood flow, as well as a corresponding decrease in systemic vascular resistance (i.e., reduced blood pressure). Tissue perfusion is a term that generally describes blood flow into the tissues.
- Vasodilation has been recognized to be beneficial in the treatment of myocardial infarction, strokes, and vascular diseases.
- Maintaining adequate tissue perfusion is recognized to be beneficial during any hypoperfused event, during any coronary syndrome including myocardial infarction, before, during, or after medical intervention (e.g., angioplasty, plastic and reconstructive surgery, maxillofacial surgery, vascular surgery, transplant surgery, or cardiac surgery); or before, during, or after dental procedures, or dermatological test patches and other skin challenges, or before, during, or after an exercise regime; or during wound healing.
- The effects of ultrasound energy upon enhanced. vasodilation and/or blood perfusion have been observed. However, the conventional use of ultrasound energy in medicine for either diagnostic or therapeutic purposes typically has involved the application of ultrasound energy at frequency ranges—e.g., about 2 MHz to 40 MHz for diagnostic purposes (ultrasound imaging), and about 1 MHz to 3 MHz (physiotherapy or diathermy devices)—and/or with attendant exposure times, that can induce thermal effects due to tissue absorption of ultrasound energy. These thermal mechanisms caused by tissue absorption of ultrasound energy can lead to substantial deep heating of tissue. Often, in typically conventional ultrasound modalities, the thermal mechanisms due to absorption of ultrasound energy in tissue can be intended and beneficial, or at least not detrimental. However, when the principal purpose of the therapy is to create vasodilation and/or sustain adequate tissue perfusion in instances where the body is undergoing, or is about to undergo, or has undergone an event that is or has the potential for challenging patient well being, unintended substantial deep tissue heating effects or other unnecessary physiologic challenges to body tissue or organs should be avoided.
- The invention provides systems and methods for applying audible acoustic energy to affect vasodilation and/or an increase in tissue perfusion. The desired physiologic effects can be achieved without substantial deep heating of tissue.
- Other features and advantages of the inventions are set forth in the following specification and attached drawings.
-
FIG. 1 is a perspective view of a system for transcutaneously applying audible acoustic energy to affect vasodilation and/or increased blood perfusion. -
FIG. 2 is an enlarged exploded perspective view of an audible acoustic energy applicator that forms a part of the system shown inFIG. 1 . -
FIG. 3 is an enlarged assembled perspective view of the audible acoustic energy applicator shown inFIG. 2 . -
FIG. 4 is a side section view of the acoustic contact area of the audible acoustic energy applicator shown inFIG. 2 . -
FIG. 5 is a view of the applicator shown inFIG. 2 held by a stabilization assembly in a secure position overlaying the sternum of a patient, to transcutaneously direct acoustic energy, e.g., toward the heart. -
FIG. 6 is a side elevation view, with portions broken away and in section, of an acoustic stack that can be incorporated into the applicator shown inFIG. 2 . -
FIG. 7 is a side elevation view, with portions broken away and in section, of an acoustic stack that can be incorporated into the applicator shown inFIG. 2 . -
FIG. 8 a to 8 c graphically depict the technical features of a frequency tuning function that the system shown inFIG. 1 can incorporate. -
FIG. 9 graphically depicts the technical features of a power ramping function that the system shown inFIG. 1 can incorporate. -
FIG. 10 is a schematic view of a controller that the system shown inFIG. 1 can incorporate, which includes a frequency selection and tuning function, a power ramping function, and an output power control function. -
FIG. 11 is a diagrammatic view of a use register chip that forms a part of the use monitoring function shown inFIG. 10 . -
FIG. 12 is a diagrammatic flow chart showing the technical features of the use monitoring function shown inFIG. 10 . - The invention may be embodied in several forms without departing from its spirit or essential characteristics. The scope of the invention is defined in the appended claims, rather than in the specific description preceding them. All embodiments that fall within the meaning and range of equivalency of the claims are therefore intended to be embraced by the claims.
- A
system 10 will be described in connection with the therapeutic indication of providing vasodilation and/or increased tissue perfusion by the transcutaneous application of audible acoustic energy. As used herein, the term “audible acoustic energy” means vibrational energy in a range of frequencies between about 20 Hz to no greater than 20 kHz. - The audible acoustic energy is desirably indicated, e.g., for the treatment of myocardial infarction, strokes, and vascular diseases; and/or before, during, or after percutaneous or surgical intervention; and/or before, during, or after dental procedures; and/or before, during, or after dermatological test patches and other skin challenges; and/or before, during, or after prescribed exercise regimes; and/or during wound healing. The
system 10 has application for use in diverse regions of the body, e.g., in the thoracic cavity, the abdomen, the arms, the legs, the neck, or the head. - I. System for Providing Noninvasive Vasodilation and/or Tissue Perfusion using Audible Acoustic Energy
-
FIG. 1 schematically shows a compact, portabletherapeutic system 10 that makes it possible to treat a person who needs or who is likely to need vasodilation and/or an increase in the flow rate to or perfusion of selected tissues. - The
system 10 includes durable and disposable equipment and materials necessary to treat the person at a designated treatment location. In use, thesystem 10 affects vasoldilation and/or increased tissue perfusion by transcutaneously applying audible acoustic energy. - As
FIG. 1 shows, thesystem 10 includes at the treatment location an audible acousticenergy generating machine 16. Thesystem 10 also includes at the treatment location at least one audibleacoustic energy applicator 18, which is coupled to themachine 16 during use. AsFIG. 5 shows, thesystem 10 also includes anassembly 12 for use with theapplicator 18 to stabilize the position of theapplicator 18 on a patient for hands-free use. In the illustrated embodiment (seeFIG. 5 ), theapplicator 18 is secured against movement on a person's thorax, overlaying the sternum, to direct acoustic energy toward the vasculature of the heart. It should be appreciated that the applicator can be sized and configured for placement on other regions of the body, such as the arms, legs, or head. The applicator can be secured to the patient as well. - The location where treatment occurs can vary. It can be a traditional clinical setting, where support and assistance by one or more medically trained care givers are immediately available to the person, such as inside a hospital, e.g., in an emergency room, catheter lab, operating room, or critical care unit. However, due to the purposeful design of the
system 10, the location need not be confined to a traditional clinical setting. The location can comprise a mobile setting, such as an ambulance, helicopter, airplane, or like vehicle used to convey the person to a hospital or another clinical treatment center. The location can even comprise an everyday, public setting, such as on a cruise ship, or at a sports stadium or airport, or a private setting, such as in a person's home, where the effects of vasoconstriction and/or low tissue perfusion can arise. - By purposeful design of durable and disposable equipment, the
system 10 can make it possible to initiate treatment of vasoconstriction and/or a reduced tissue perfusion incident in a non-clinical, even mobile location, outside a traditional medical setting. The system thereby makes effective use of the critical time period before the person enters a hospital or another traditional medical treatment center. - The features and operation of the
system 10 will now be described in greater detail. - A. The Audible Acoustic Energy Generator
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FIG. 1 shows a representative embodiment of the audible acousticenergy generating machine 16. Themachine 16 can also be called an “audible acoustic energy generator.” Themachine 16 is intended to be a durable item capable of long term, maintenance free use. - As shown in
FIG. 1 , themachine 16 can be variously sized and shaped to present a lightweight and portable unit, presenting a compact footprint suited for transport. Themachine 16 can be sized and shaped to be mounted at bedside, or to be placed on a table top or otherwise occupy a relatively small surface area. This allows themachine 16 to travel with the patient within an ambulance, airplane, helicopter, or other transport vehicle where space is at a premium. This also makes possible the placement of themachine 16 in a non-obtrusive way within a private home setting, such as for the treatment of chronic angina. - In the illustrated embodiment, the
machine 16 includes achassis 22, which, for example, can be made of molded plastic or metal or both. Thechassis 22 houses amodule 24 for generating electric signals. The signals are conveyed to theapplicator 18 by aninterconnect 30 to be transformed into acoustic energy. Acontroller 26, also housed within the chassis 22 (but which could be external of thechassis 22, if desired), is coupled to themodule 24 to govern the operation of themodule 24. Further desirable technical features of thecontroller 26 will be described later. - The
machine 16 also preferably includes anoperator interface 28. Using theinterface 28, the operator inputs information to thecontroller 26 to affect the operating mode of themodule 24. Through theinterface 28, thecontroller 26 also outputs status information for viewing by the operator. Theinterface 28 can provide a visual readout, printer output, or an electronic copy of selected information regarding the treatment. Theinterface 28 is shown as being carried on thechassis 22, but it could be located external of thechassis 22 as well. - The
machine 16 includes apower cord 14 for coupling to a conventional electrical outlet, to provide operating power to themachine 16. Themachine 16 can also include a battery module (not shown) housed within thechassis 22, which enables use of themachine 16 in the absence or interruption of electrical service. The battery module can comprise rechargeable batteries, which can be built in thechassis 22 or, alternatively, be removed from thechassis 22 for recharge. Likewise, the battery module (or themachine 16 itself) can include a built-in or removable battery recharger. Alternatively, the battery module can comprise disposable batteries, which can be removed for replacement. - Power for the
machine 16 can also be supplied by an external battery and/or line power module outside thechassis 22. The battery and/or line power module is releasably coupled at time of use to the components within thechassis 22, e.g., via a power distribution module within thechassis 22. - The provision of battery power for the
machine 16 frees themachine 16 from the confines surrounding use of conventional ultrasound equipment, caused by their dependency upon electrical service. This feature makes it possible for themachine 16 to provide a treatment modality that continuously “follows the patient,” as the patient is being transported to or inside a transport vehicle, or as the patient is being shuttled between different locations within a treatment facility, e.g., from the emergency room to a catheterization lab or holding area within or outside the emergency room. - In a representative embodiment, the
chassis 22 measures about 12 inches×about 8 inches×about 8 inches and weighs about 9 pounds. - B. The Audible Acoustic Energy Applicator
- As shown in
FIG. 5 , theapplicator 18 can also be called the “patient interface.” Theapplicator 18 comprises the link between themachine 16 and the treatment site within the thoracic cavity of the person undergoing treatment. Theapplicator 18 converts electrical signals from themachine 16 to acoustic energy, and further directs the acoustic energy to the targeted treatment site. - Desirably, the
applicator 18 is intended to be a disposable item. At least oneapplicator 18 is coupled to themachine 16 via theinterconnect 30 at the beginning a treatment session. Theapplicator 18 is preferably decoupled from the interconnect 30 (asFIG. 1 shows) and discarded upon the completing the treatment session. However, if desired, theapplicator 18 can be designed to accommodate more than a single use. - As
FIGS. 2 and 3 show, the audibleacoustic energy applicator 18 includes a shaped metal orplastic body 38 ergonomically sized to be comfortably grasped and manipulated in one hand. Thebody 38 houses and supports at least one audible acoustic energy transducer 40 (seeFIG. 3 ). - In the illustrated embodiment, the audible
acoustic energy transducer 40 comprises anacoustic stack 20. Theacoustic stack 20 comprises afront mass piece 32, aback mass piece 34, and one or morepiezoelectric elements 36, which are bolted together. Theback mass piece 34 comprises an annular ring of material having relatively high acoustic impedance, e.g., steel or stainless steel. “Acoustic impedance” is defined as the product. of the density of the material and the speed of sound. - The
front mass piece 32 comprises a cone-shaped piece of material having relatively low acoustic impedance, e.g., aluminum or magnesium. Thepiezoelectric elements 36 are annular rings made of piezoelectric material, e.g., PZT. An internally threaded hole or the like receives abolt 42 that mechanically biases theacoustic stack 20. Abolt 42 that can be used for this purpose is shown in U.S. Pat. No. 2,930,912. Thebolt 42 can extend entirely through thefront mass piece 32 or, thebolt 42 can extend through only a portion of the front mass piece 32 (seeFIG. 7 ). - In an alternative embodiment (see
FIG. 6 ), theacoustic stack 20′ of atransducer 40′ can comprise a singlepiezoelectric element 36′ sandwiched between front and backmass pieces 32′ and 34′. In this arrangement, theback mass piece 34′ is electrically insulated from thefront mass piece 32′ by, e.g., an insulating sleeve andwasher 44. - The piezoelectric element(s) 36/36′ have electrodes 46 (see
FIG. 2 ) on major positive and negative flat surfaces. Theelectrodes 46 electrically connect theacoustic stack 20 of thetransducer 40 to the electricalsignal generating module 24 of themachine 16. When electrical energy at an appropriate frequency is applied to theelectrodes 46, thepiezoelectric elements 36/36′ convert the electrical energy into mechanical (i.e., acoustic) energy in the form of mechanical vibration. - The mechanical vibration created by the
transducer 40/40′ is coupled to a patient through atransducer bladder 48, which rests on a skin surface. Thebladder 48 defines a bladder chamber 50 (seeFIG. 4 ) between it and thefront mass piece 32. Thebladder chamber 50 spaces the front mass piece 32 a set distance from the patient's skin. Thebladder chamber 50 accommodates a volume of an acoustic coupling media liquid, e.g., liquid, gel, oil, or polymer, that is conductive to acoustic energy, to further cushion the contact between theapplicator 18 and the skin. The presence of the acoustic coupling media also makes the acoustic contact area of thebladder 48 more conforming to the local skin topography. - Desirably, an acoustic coupling medium is also applied between the
bladder 48 and the skin surface. The coupling medium can comprise, e.g., a gel material (such as AQUASONIC® 100, by Parker Laboratories, Inc., Fairfield, N.J.). The external material can possess sticky or tacky properties, to further enhance the securement of theapplicator 18 to the skin. - In the illustrated embodiment, the
bladder 48 andbladder chamber 50 together form an integrated part of theapplicator 18. Alternatively, thebladder 48 andbladder chamber 50 can be formed by a separate molded component, e.g., a gel or liquid filled pad, which is supplied separately. A molded gel filled pad adaptable to this purpose is the AQUAFLEX® Ultrasound Gel Pad sold by Parker Laboratories (Fairfield, N.J.). - In a representative embodiment, the
front mass piece 32 of theacoustic stack 20 measures about 2 inches in diameter, whereas the acoustic contact area formed by thebladder 48 measures about 5 inches in diameter. Anapplicator 18 that presents an acoustic contact area of larger diameter than thefront mass piece 32 of thetransducer 40 provides a propagation path for the diverging acoustic beam. Also, a large contact area provides additional stability (with the assembly 12) in hands-free use. In a representative embodiment, theapplicator 18 measures about 5 inches in diameter about thebladder 48, about 5 inches in height, and weighs about one pound. - Desirably, when used to apply audible acoustic energy transcutaneously, the diameter of the
front mass piece 32 is sized to deliver acoustic energy in a desired range of fundamental frequencies to substantially the entire targeted region. Desirably, the fundamental frequencies lay in a frequency range of about 20 Hz to about 20 kHz, and most desirably, in a range of between 15 kHz and 20 kHz. - Within this range of fundamental frequencies, if the targeted region is, e.g., the thoracic cavity including the heart, the
applicator 18 should be sized to percutaneously transmit the energy in a diverging beam, which substantially covers the entire heart and coronary circulation. Theapplicator 18 may comprise a single transducer or an array of transducers that together form an acoustic contact area. - Normal hearts vary significantly in size and distance from skin between men and women, as well as among individuals regardless of sex. Typically, for men, the size of a normal heart ranges between 8 to 11 cm in diameter and 6 to 9 cm in depth, and the weight ranges between 300 to 350 grams. For men, the distance between the skin and the anterior surface of the heart (which will be called the “subcutaneous depth” of the heart) ranges between 4 to 9 cm. Typically, for women, the size of a normal heart ranges between 7 to 9 cm in diameter and 5 to 8 cm in depth, and the weight ranges between 250 to 300 grams. For women, the subcutaneous depth of the heart ranges between 3 to 7 cm.
- The degree of divergence or “directivity” of the acoustic beam transmitted percutaneously through the acoustic contact area is a function of the wavelength of the energy being transmitted. Generally speaking, as the wavelength increases, the beam divergence becomes larger (given a fixed aperture size). If the beam divergence at the subcutaneous depth of the heart is less than beam area of the heart, the audible acoustic energy will not be delivered to substantially the whole heart. Therefore, the beam divergence should desirably be essentially equal to or greater than the targeted beam area at the subcutaneous depth of the heart.
- Within the desired range of fundamental frequencies of 20 Hz to 20 kHz, the beam divergence can be expressed in terms of an aperture size measured in wavelengths. The aperture size (AP) can be expressed as a ratio between the effective diameter of the front mass piece 32 (D) and the wavelength of the acoustic energy being applied (WL), or AP=D/WL. The term “effective diameter” is intended to encompass a geometry that is “round,” as well as a geometry that is not “round”, e.g., being elliptical or rectilinear, but which possesses a surface area in contact with skin that can be equated to an equivalent round geometry of a given effective diameter.
- For the desired range of fundamental frequencies of 20 Hz to about 20 kHz, front
mass pieces 32 characterized by aperture sizes laying within a range of 0.5 to 5 wavelengths, and preferably less than 2 wavelengths, possess the requisite degree of beam divergence to transcutaneously deliver audible acoustic energy from a position on the thorax, and preferably on or near the sternum, to substantially an entire normal heart of a man or a woman. - Of course, using the same criteria, the
transducer face 46 can be suitably sized for other applications within the thoracic cavity or elsewhere in the body. For example, thefront mass piece 32 can be sized to delivery energy to beyond the heart and the coronary circulation, to affect the pulmonary circulation. - An O-ring 52 (see
FIG. 4 ) is captured within agroove 54 in thebody 38 of theapplicator 18 and agroove 84 on thefront mass piece 32 of thetransducer 40. The O-ring 52 seals thebladder chamber 50 and prevents liquid in thechamber 50 from contacting the sides of thefront mass piece 32. Thus, asFIG. 4 shows, only the radiating surface of thefront mass piece 32 is in contact with the acoustic coupling medium within thechamber 50. - Desirably, the material of the O-
ring 52 is selected to possess elasticity sufficient to allow theacoustic stack 20 of thetransducer 40 to vibrate freely in a piston-like fashion within thetransducer body 38. Still, the material of the O-ring 52 is selected to be sturdy enough to prevent theacoustic stack 20, while vibrating, from popping out of thegrooves - In a representative embodiment, the O-
ring 52 is formed from nitrile rubber (Buna-N) having a hardness of about 30 Shore A to about 100 Shore A. Preferably, the O-ring 52 has a hardness of about 65 Shore A to about 75 Shore A. - The
bladder 48 is stretched across the face of thebladder chamber 50 and is preferably also locked in place with another O-ring 56 (seeFIG. 4 ). A membrane ring may also be used to prevent the O-ring 56 from popping loose. The membrane ring desirably has a layer or layers of soft material (e.g., foam) for contacting the skin. - Localized skin surface heating effects may arise in the presence of air bubbles trapped between the acoustic contact area (i.e., the surface of the bladder 48) and the individual's skin. In the presence of air bubbles acoustic energy may cause cavitation and result in heating at the skin surface. To minimize the collection of air bubbles along the acoustic contact area, the
bladder 48 desirably presents a flexible, essentially flat radiating surface contour where it contacts the individual's skin (seeFIG. 4 ), or a flexible, outwardly bowed or convex radiating surface contour (i.e., curved away from the front mass piece) where it contacts with or conducts acoustic energy to the individual's skin. Either a flexible flat or convex surface contour can “mold” evenly to the individual's skin topography, to thereby mediate against the collection and concentration of air bubbles in the contact area where skin contact occurs. - To further mediate against cavitation-caused localized skin surface heating, the interior of the
bladder chamber 50 can include a recessedwell region 58 surrounding thefront mass piece 32. Thewell region 58 is located at a higher gravity position than the plane of thefront mass piece 32. Air bubbles that may form in fluid located in thebladder chamber 50 are led by gravity to collect in thewell region 58 away from the acoustic energy beam path. - The
front mass piece 32 desirably possesses either a flat radiating surface (asFIG. 4 shows) or a convex radiating surface (asFIG. 7 shows). The convex radiation surface directs air bubbles off the radiating surface. The radiating surface of the front mass piece may also be coated with a hydrophilic material 60 (seeFIG. 4 ) to prevent air bubbles from sticking. - The
transducer 40 may also include a reflux valve/liquid inlet port 62. - The
interconnect 30 carries a distal connector 80 (seeFIG. 2 ), designed to easily plug into a mating outlet in theapplicator 18. Aproximal connector 82 on theinterconnect 30 likewise easily plugs into a mating outlet on the chassis 22 (seeFIG. 1 ) , which is itself coupled to thecontroller 26. In this way, theapplicator 18 can be quickly connected to themachine 16 at time of use, and likewise quickly disconnected for discard once the treatment session is over. Other quick-connect coupling mechanisms can be used. It should also be appreciated that theinterconnect 30 can be hard wired as an integrated component to theapplicator 18 with a proximal quick-connector to plug into thechassis 22, or, vice versa, theinterconnect 30 can be hard wired as an integrated component to thechassis 22 with a distal quick-connector to plug into theapplicator 18. - As
FIG. 5 shows, thestabilization assembly 12 allows the operator to temporarily but securely mount theapplicator 18 against an exterior skin surface for use. In the illustrated embodiment, since the treatment site exists in the thoracic cavity, theattachment assembly 54 is fashioned to secure theapplicator 18 on the person's thorax, overlaying the sternum or breastbone, asFIG. 5 shows. - The
assembly 12 can be variously constructed. As shown inFIG. 5 , theassembly 12 comprisesstraps 90 that pass throughbrackets 92 carried by theapplicator 18. Thestraps 90 encircle the patient's neck and abdomen. - Just as the
applicator 18 can be quickly coupled to themachine 16 at time of use, thestabilization assembly 12 also preferably makes the task of securing and removing theapplicator 18 on the patient simple and intuitive. Thus, thestabilization assembly 12 makes it possible to secure theapplicator 18 quickly and accurately in position on the patient in cramped quarters or while the person (and thesystem 10 itself) is in transit. - II. Controlling the Application of Audible Acoustic Energy
- The
system 10 applies audible acoustic energy to achieve vasodilation and/or an increase tissue perfusion without causing substantial deep tissue heating. To achieve the optimal application of audible acoustic energy and this optimal therapeutic effect, thesystem 10 incorporates selection and tuning of an output frequency. Thesystem 10 can also incorporate other features such as power ramping, output power control, and the application of audible acoustic energy at the selected frequency in pulses. - A. Selection of Output Frequency
- Depending upon the treatment parameters and outcome desired, the
controller 26 desirably operates a giventransducer 40 at a fundamental frequency in the range of about 20 kHz or less. Desirably, the fundamental frequencies lay in a frequency range of about 20 Hz to 20 kHz, and desirably within a range of 15 kHz to 20 kHz. - The
applicator 18 can include multiple transducers 40 (ormultiple applicators 18 can be employed simultaneously for the same effect), which can be individually conditioned by thecontroller 26 for operation. One ormore transducers 40 within an array oftransducers 40 can be operated, e.g., at different fundamental frequencies. For example, one ormore transducers 40 can be operated at about 15 kHz, while another one ormore transducers 40 can be operated at about 20 kHz. More than two different fundamental frequencies can be used, e.g., about 15 kHz, about 18 kHz, and about 20 kHz. - The
controller 26 can trigger the fundamental frequency output according to time or a physiological event (such as ECG or respiration). - As
FIG. 10 shows, thecontroller 26 desirably includes atuning function 64. Thetuning function 64 selects an optimal frequency at the outset of each treatment session. In the illustrated embodiment (seeFIGS. 8A to 8C), the tuning function sweeps the output frequency within a predetermined range of frequencies (f-start to f-stop). The frequency sweep can be and desirably is done at an output power level that is lower than the output power level of treatment (seeFIG. 9 ). The frequency sweep can also be done in either a pulsed or a continuous mode, or in a combination of these two modes. An optimal frequency of operation is selected based upon one or more parameters sensed during the sweeping operation. - As
FIG. 8A shows, the frequency sweep can progress from a lower frequency (f-start) to a higher frequency (f-stop), or vice versa. The sweep can proceed on a linear basis (asFIG. 8A also shows), or it can proceed on a non-linear basis, e.g., logarithmically or exponentially or based upon another mathematical function. The range of the actual frequency sweep may be different from the range that is used to determine the frequency of operation. For instance, the frequency span used for the determination of the frequency of operation may be smaller than the range of the actual sweep range. - In one frequency selection approach (see
FIGS. 8A and 8C ), while sweeping frequencies, thetuning function 64 adjusts the output voltage and/or current to maintain a constant output power level (p-constant). Thefunction 64 also senses changes in transducer impedance (seeFIG. 8B )—Z-min to Z-max—throughout the frequency sweep. In this approach (seeFIG. 8B ), thetuning function 64 selects as the frequency of operation the frequency (f-tune) where, during the sweep, the minimum magnitude of transducer impedance (Z-min) is sensed. Typically, this is about the same as the frequency of maximum output current (I), which in turn, is about the same as the frequency of minimum output voltage (V). - In an alternative frequency selection approach, the
tuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum of real part (R) of transducer impedance (Z) occurs, where:
|Z|=√(R 2 +X 2) - and where |Z| is the absolute value of the transducer impedance (Z), which derived according to the following expression:
Z=R+iX - where R is the real part, and X is the imaginary part.
- In another alternative frequency selection approach, while sweeping the frequencies, the
tuning function 64 can maintain a constant output voltage. In this approach, thetuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum output power occurs. Alternatively, thetuning function 64 can select as the frequency of operation the frequency where, during the sweep, the maximum output current occurs. - B. Power Ramping
- As before described, the
tuning function 64 desirably operates at an output power level lower than the power level of treatment. In this arrangement, once the operating frequency has been selected, the output power level needs to be increased to the predetermined output level to have the desired therapeutic effect. - In the illustrated embodiment (see
FIG. 10 ), thecontroller 26 desirably includes a rampingfunction 66. The ramping function 66 (seeFIG. 9 ) causes a gradual ramp up of the output power level at which thetuning function 64 is conducted (e.g., 5 W) to the power level at which treatment occurs (e.g., 25 W). The gradual ramp up decreases the possibility of unwanted patient reaction to the acoustic exposure. Further, a gradual ramp up is likely to be more comfortable to the patient than the sudden onset of the full output power. - In a desired embodiment, the ramping
function 66 increases power at a rate of about 0.01 W/s to about 10 W/s. A particularly desired ramping rate is between about 0.1 W/s to about 5 W/s. The rampingfunction 66 desirably causes the ramp up in a linear fashion (asFIG. 9 shows). However, the ramping function can employ non-linear ramping schemes, e.g., logarithmic or according to another mathematical function. - C. Output Power Control
- Also depending upon the treatment parameters and outcome desired, the
controller 26 can operate a giventransducer 40 at a prescribed power level, which can remain fixed or can be varied during the treatment session. Thecontroller 26 can also operate one ormore transducers 40 within an array of transducers 40 (or when using multiple applicators 18) at different power levels, which can remain fixed or themselves vary over time. - The parameters affecting power output take into account the output of the signal generator module; the physical dimensions and construction of the applicator; and the physiology of the tissue region to which acoustic energy is being applied.
- More particularly, the parameters affecting power output can take into account the output of the
signal generator module 24; the physical dimensions and construction of theapplicator 18; and the physiology of the tissue region to which acoustic energy is being applied. In the context of the illustrated embodiment, these parameters include the total output power (PTotal) (expressed in watts—W) provided to thetransducer 40 by thesignal generator module 24; the intensity of the power (expressed in watts per square centimeter—W/cm2) in the effective radiating area of theapplicator 18, which takes into account the total power PTotal, and the area of thebladder 48; and the peak rarefactional acoustic pressure (Ppeak(Neg)) (expressed in Pascals—Pa) that the tissue experiences, which takes into consideration that the physiological tolerance of tissue to rarefactional pressure conditions is much less than its tolerance to compressional pressure conditions. PPeak(Neg) can be derived as a known function of W/cm2. - In one embodiment, the
applicator 18 can be sized to provide an intensity equal to or less than 25 W/cm2 at a maximum total power output of equal to or less than 200 W (most preferably 15 W. PTotal 150 W) operating at a fundamental frequency of less than or equal to 20 kHz. Audible acoustic energy within the range of fundamental frequencies specified passes through bone, while also providing selectively different mechanical effects (depending upon the frequency), and without substantial deep tissue heating effects, as previously described. Power supplied within the total power output range specified meets the size, capacity, and cost requirements of battery power, to make a transportable, “follow the patient” treatment modality possible, as already described. Audible acoustic energy supplied within the power density range specified keeps peak rarefactional acoustic pressure within physiologically tolerable levels. Theapplicator 18 meeting these characteristics can therefore be beneficially used in conjunction with the transportable audibleenergy generator machine 16, as described. - During a given treatment session, the transducer impedance may vary due to a number of reasons, e.g., transducer heating, changes in acoustic coupling between the transducer and patient, and/or changes in transducer bladder fill volume, for instance, due to degassing. In the illustrated embodiment (see
FIG. 10 ), thecontroller 26 includes an outputpower control function 68. The outputpower control function 68 holds the output power constant, despite changes in transducer impedance within a predetermined range. If the transducer falls out of the predetermined range, for instance, due to an open or short circuit, thecontroller 26 shuts down the generator audibleacoustic energy module 24 and desirably sounds an alarm. - Governed by the output
power control function 68, as the transducer impedance increases, the output voltage is increased to hold the power output constant. Should the output voltage reach a preset maximum allowable value, the output power will decrease, provided the transducer impedance remains within its predetermined range. As the transducer impedance subsequently drops, the output power will recover, and the full output power level will be reached again. - Governed by the output
power control function 68, as the transducer impedance decreases, the output current is increased to hold the power output constant. Should the output current reach a preset maximum allowable value, the output power will decrease until the impedance increases again, and will allow full output power. - In addition to the described changes in the output voltage and current to maintain a constant output power level, the output
power control function 68 can vary the frequency of operation slightly upward or downward to maintain the full output power level within the allowable current and voltage limits. - D. Pulsed Power Mode
- The application of audible acoustic energy in a pulsed power mode serves, in conjunction with the selection of the fundamental output frequency, to reduce deep heating tissue effects. This is because, at a given frequency, a high acoustic intensity, or high acoustic power, results in more deep heating of tissue than a low intensity, or power. At the same peak acoustic intensity, the pulse mode application of acoustic energy results in less deep heating of tissue than continuous mode because tissue is cooled off in between the pulses. During the pulsed power mode, audible acoustic energy is applied at a desired fundamental frequency or within a desired range of fundamental frequencies at the prescribed power level or range of power levels (as described above, to achieve the desired physiological effect) in a prescribed duty cycle (DC) (or range of duty cycles) and a prescribed pulse repetition frequency (PRF) (or range of pulse repetition frequencies). Desirably, the pulse repetition frequency (PRF) is between about 20 Hz to about 50 Hz (i.e., between about 20 pulses a second to about 50 pulses a second).
- The duty cycle (DC) is equal to the pulse duration (PD) divided by one over the pulse repetition frequency (PRF). The pulse duration (PD) is the amount of time for one pulse. The pulse repetition frequency (PRF) represents the amount of time from the beginning of one pulse to the beginning of the next pulse. For example, given a pulse repetition frequency (PRF) of 30 Hz (30 pulses per second) and a duty cycle of 25% yields a pulse duration (PD) of approximately 8 ms pulse followed by a 25 ms off
period 30 times per second. - Given a pulse repetition frequency (PRF) selected at 25 Hz and a desired fundamental frequency between about 15 kHz and 20 kHz delivered in a power range between about 5 to 30 W, a duty cycle of about 50% or less meets the desired physiological objectives with less incidence of localized conductive heating effects compared to a continuous application of the same fundamental frequency and power levels over a comparable period of time. Given these operating conditions, the duty cycle desirably lays in a range of between about 1% and about 35%.
- III. Monitoring use of the Transducer
- To protect patients from the potential adverse consequences occasioned by multiple use, which include disease transmission, or material stress and instability, or decreased or unpredictable performance, the
controller 26 desirably includes a use monitoring function 70 (seeFIG. 10 ) that monitors incidence of use of a giventransducer 40. - In the illustrated embodiment, the
transducer 40 carries a use register 72 (seeFIG. 4 ). Theuse register 72 is configured to record information before, during, and after a given treatment session. Theuse register 72 can comprise a solid state micro-chip, ROM, EEROM, EPROM, or non volatile RAM (NVRAM) carried by thetransducer 40. - The
use register 72 is initially formatted and programmed by the manufacturer of the system to include memory fields. In the illustrated embodiment (seeFIG. 11 ), the memory fields of the use register are of two general types: Write Many Memory Fields 74 and Write-Once 10Memory Fields 76. The Write Many Memory Fields 74 record information that can be changed during use of thetransducer 40. The Write-Once Memory Fields 76 record information that, once recorded, cannot be altered. - The specific information recorded by the Memory 15
Fields Many Memory Fields 74.Field Size Name Description Location (Byte) Treatment If a transducer has been used for a 0 1 Complete prescribed maximum treatment time (e.g., 60 minutes), the treatment complete flag is set to 1 otherwise it is zero. Prescribed This is the allowable usage time of 1-2 2 Maximum the transducer. This is set by the Treatment manufacturer and determines at what Time point the Treatment Complete flag (Minutes) is set to 1. Elapsed Initialized to zero. This area is 3-4 2 Usage Time then incremented every minute that (Minutes) the system is transmitting acoustic energy. This area keeps track of the amount of time that the transducer has been used. When this time reaches the Prescribed Maximum Treatment Time, the Treatment Complete flag is set to 1. Transducer This is an area that could be used 5-6 2 Frequency to prescribe the operational frequency of the transducer, rather than tuning the transducer to an optimal frequency, as above described. In the latter instance, this area shows the tuned frequency once the transducer has been tuned. Average The system reads and accumulates 7-8 2 Power the delivered power throughout the (Watts) procedure. Every minute, the average power number is updated in this area from the system, at the same time the Elapsed Usage Time is updated. when the Usage time clock is updated. This means that the average power reading could be off by a maximum of 59 seconds if the treatment is stopped before the Treatment Complete flag is set. This average power can be used as a check to make sure that the system was running at full power during the procedure. Applicator Use Register CRC. This desirably 9-10 2 CRC uses the same CRC algorithm used to protect the controller ROM. Copyright Desirably, the name of the 11-23 11 Notice manufacturer is recorded in this area. Other information can be recorded here as well. - The on/off cycles of acoustic energy transmission could affect the accuracy of the recorded power levels because of the variance of the power levels due to ramping
function 66. For this reason it may be advantageous to also record the number of on/off cycles of acoustic energy transmission. This will help explain any discrepancies in the average power reading. It might also allow the identification of procedural problems with system use. - Each use register 72 can be assigned a unique serial number that could be used to track transducers in the field. This number can be read by the
use monitoring function 70 if desired. - The following table exemplifies typical types of information that can be recorded in the Write-
Once Memory Fields 76.Field Size Name Description Location (Byte) Treatment If a transducer has been used for 0 1 Complete a prescribed maximum treatment time (e.g., 60 minutes), the treatment complete flag is set to 1 otherwise it is zero. Prescribed This is the allowable usage time 1-2 2 Maximum of the transducer. This is set by Treatment the manufacturer and determines at Time what point the Treatment Complete (Minutes) flag is set to 1. Elapsed Initialized to zero. This area 3-4 2 Usage Time is then incremented every minute (Minutes) that the system is transmitting acoustic energy. This area keeps track of the amount of time that the transducer has been used. When this time reaches the Prescribed Maximum Treatment Time, the Treatment Complete flag is set to 1. Transducer This is an area that could be 5-6 2 Frequency used to prescribe the operational frequency of the transducer, rather than tuning the transducer to an optimal frequency, as above described. In the latter instance, this area shows the tuned frequency once the transducer has been tuned. Average The system reads and accumulates 7-8 2 Power the delivered power throughout the (Watts) procedure. Every minute, the average power number is updated in this area from the system, at the same time the Elapsed Usage Time is updated. When the Usage time clock is updated. This means that the average power reading could be off by a maximum of 59 seconds if the treatment is stopped before the Treatment Complete flag is set. This average power can be used as a check to make sure that the system was running at full power during the procedure. Applicator Use Register CRC. This desirably 9-10 2 CRC uses the same CRC algorithm used to protect the controller ROM. Copyright Desirably, the name of the 11-23 11 Notice manufacturer is recorded in this area. Other information can be recorded here as well. - The on/off cycles of acoustic energy transmission could affect the accuracy of the recorded power levels because of the variance of the power levels due to ramping
function 66. For this reason it may be advantageous to also record the number of on/off cycles of acoustic energy transmission. This will help explain any discrepancies in the average power reading. It might also allow the identification of procedural problems with system use. - Each use register 72 can be assigned a unique serial number that could be used to track transducers in the field. This number can be read by the
use monitoring function 70 if desired. - The following table exemplifies typical types of information that can be recorded in the Write-
Once Memory Fields 76.Size Field Name Description (Bytes) Start Date Once the system has tuned the transducer Time and started to transmit acoustic energy, the current date and time are written to this area. This area is then locked, which prevents the data from ever-being changed. Tuned The tuned frequency is written to this Frequency location when the Start Date and Time is set. This prevents this information from being written over on subsequent tunes (if necessary). - As
FIG. 12 shows, when atransducer 40 is first coupled to themachine 16, and prior to enabling the conveyance of audible acoustic energy to thetransducer 40, theuse monitoring function 70 prompts theuse register 72 to output resident information recorded in the memory fields. - The
use monitoring function 70 compares the contents of the Copyright Notice field to a prescribed content. In the illustrated embodiment, the prescribed content includes information contained in the Copyright Notice field of the WriteMany Memory Fields 74. The prescribed content therefore includes the name of the manufacturer, or other indicia uniquely associated with the manufacture. If the prescribed content is missing, theuse monitoring function 70 does not enable use of thetransducer 40, regardless of the contents of any other memory field. Thetransducer 40 is deemed “invalid.” In this way, a manufacturer can assure that only transducers meeting its design and quality control standards are operated in association with themachine 16. - If the contents of the Copyright Notice field match, the
use monitoring function 70 compares the digital value residing in the Treatment Complete field of the Write Many Memory Fields 74 to a set value that corresponds to a period of no prior use or a prior use less than the Prescribed Maximum Treatment Time—i.e., in the illustrated embodiment, a zero value. A different value (i.e., a 1 value) in this field indicates a period of prior use equal to or greater than the Prescribed Maximum Treatment Time. In this event, theuse monitoring function 70 does not enable use of thetransducer 40. Thetransducer 40 is deemed “invalid.” - If a value of zero resides in the Treatment Complete field, the
use monitoring function 70 compares the date and time data residing in the Write-Once Start Date and Time field to the current date and time established by a Real Time Clock. If the Start Date and Time is more than a prescribed time before the Real Time (e.g., 4 hours), the controller does not enable use of thetransducer 40. Thetransducer 40 is deemed “invalid.” - If the Start Date and Time field is empty, or if it is less than the prescribed time before the Real Time, the
use monitoring function 70 deems thetransducer 40 to be “valid” (providing the preceding other criteria have been met). Theuse monitoring function 70 reports a valid transducer to thecontroller 26, which initiates thetuning function 64. If the Start Date and Time field is empty, once the tuningfunction 64 is completed, the controller prompts theuse monitoring function 70 to records the current date and time in the Start Date and Time Field, as well as the selected operating frequency in the Tuned Frequency field. Thecontroller 26 then proceeds to execute the rampingfunction 66 and, then, execute the prescribed treatment protocol. - If the Start Date and Time field is not empty (indicating a permitted prior use), once the tuning
function 64 is completed, thecontroller 26 immediately proceeds with the rampingfunction 66 and, then, execute the treatment protocol. - During use of the
transducer 40 to accomplish the treatment protocol, theuse monitoring function 70 periodically updates the Elapsed Usage Time field and Average Power field (along with other Many Write Memory Fields). Once the Treatment Complete flag is set to a 1 value (indicating use of the transducer beyond the Prescribed Maximum Treatment Time), theuse monitoring function 70 interrupts the supply of energy to the transducer. Thetransducer 40 is deemed “invalid” for subsequent use. Theuse monitoring function 70 can also generate an output that results in a visual or audible alarm, informing the operator that thetransducer 40 cannot be used. - The information recorded in the
use register 72 can also be outputted to monitor use and performance of a giventransducer 40. Other sensors can be used, e.g., atemperature sensor 78 carried on the front mass piece 32 (seeFIG. 4 ), in association with the use register. - As described, the
use register 72 allows specific pieces of information to be recorded before, during and after a treatment is complete. Information contained in theuse register 72 is checked before allowing use of a giventransducer 40. Theuse register 72 ensures that only atransducer 40 having the desired design and performance criteria imparted by the manufacturer can be used. In addition, theuse register 72 can be used to “lock out” atransducer 40 and prevent it from being used in the future. The only way thetransducer 40 could be reused is to replace theuse register 72 itself. However, copying the architecture of the use register 72 (including the contents of the Copyright Message field required for validation) itself constitutes a violation of the manufacturer's copyright in a direct and inescapable way. - IV. Use with a Therapeutic Agent
- The
system 10 can be further include at the treatment location a delivery system for introducing a therapeutic agent in conjunction with the use of theapplicator 18 andmachine 16. In this arrangement, the effect of vasodilation and/or increased tissue perfusion caused by the application of audible acoustic energy can also be enhanced by the therapeutic effect of the agent, or vice versa. - A. Use with a Thrombolytic Agent
- For example, the therapeutic agent can comprise a thrombolytic agent. In this instance, the thrombolytic agent is introduced into a thrombosis site, prior to, in conjunction with, or after the application of audible acoustic energy. The interaction between the applied audible acoustic energy and the thrombolytic agent is observed to assist in the breakdown or dissolution of the trombi, compared with the use of the thrombolytic agent in the absence of audible acoustic energy. This phenomenon is discussed, e.g., in Carter U.S. Pat. No. 5,509,896; Siegel et al U.S. Pat. No. 5,695,460; and Lauer et al U.S. Pat. No. 5,399,158, which are each incorporated herein by reference.
- The process by which thrombolysis is affected by use of audible acoustic energy in conjunction with a thrombolytic agent can vary according to the frequency, power, and type of acoustic energy applied, as well as the type and dosage of the thrombolytic agent. The application of acoustic energy has been shown to cause reversible changes to the fibrin structure within the thrombus, increased fluid dispersion into the thrombus, and facilitated enzyme kinetics. These mechanical effects beneficially enhance the rate of dissolution of thrombi. In addition, cavitational disruption, acoustic radiation pressure and streaming effects can also assist in the breakdown and dissolution of thrombi.
- The type of thrombolytic agent used can vary. The thrombolytic agent can comprise a drug known to have a thrombolytic effect, such as t-PA, TNKase, or RETAVASE. Alternatively (or in combination), the agent can comprise an anticoagulant, such as heparin; or an antiplatelet drug, such as GP IIb IIIa inhibitor; or a fibrinolytic drug; or a non-prescription agent having a known beneficial effect, such as aspirin. Alternatively (or in combination), the thrombolytic agent can comprise microbubbles, which can be acoustically activated; or microparticles, which contain albumin.
- The syndrome being treated can also vary, according to the region of the body. For example, in the thoracic cavity, the thrombolytic syndrome can comprise acute myocardial infarction, or acute coronary syndrome. The syndrome can alternatively comprise suspect myocardial ischemia, prinzmetal angina, chronic angina, or pulmonary embolism.
- The thrombolytic agent is typically administered by a delivery system intravenously prior to or during the application of acoustic energy. The dosage of the thrombolytic agent is determined by the physician according to established treatment protocols.
- It may be possible to reduce the typical dose of thrombolytic agent when acoustic energy is also applied. It also may be possible to use a less expensive thrombolytic agent or a less potent thrombolytic agent when acoustic energy is applied. The ability to reduce the dosage of thrombolytic agent, or to otherwise reduce the expense of thrombolytic agent, or to reduce the potency of thrombolytic agent, when audible acoustic energy is also applied, can lead to additional benefits, such as decreased complication rate, an increased patient population eligible for the treatment, and increased locations where the treatment can be administered (i.e., outside hospitals and critical care settings, as well as in private, in-home settings).
- B. Use with an Angiogenic Agent
- Treatment using audible acoustic energy alone can simulate additional capillary or microcirculatory activity, resulting in an arteriogenesis/angiogenesis effect. This treatment can be used as an adjunct to treatment using angiogenic agents released in the coronary circulation to promote new arterial or venous growth in ischemic cardiac tissue or elsewhere in the body. In this instance, the therapeutic agent can comprise an angiogenic agent, e.g., Monocyte Chemoattractant Protein-1, or Granulocyte-Macrophage Colony-Stimulating-Factor.
- It is believed that the angiogenic effects of these agents can be enhanced by shear-related phenomena associated with increased blood flow through the affected area. Increased blood perfusion in the heart caused by the application of audible acoustic energy can induce these shear-related phenomena in the presence of the angiogenic agents, and thereby lead to increased arterial-genesis and/or vascular-genesis in ischematic heart tissue.
- C. Use of the System with other Treatment Applications
- The
system 10 can be used to carry out other therapeutic treatment objectives, as well. - For example, the
system 10 can be used to carry out cardiac rehabilitation. The repeated application of audible acoustic energy over an extended treatment period can exercise and strengthen heart muscle weakened by disease or damage. As another example, treatment using audible acoustic energy can facilitate an improvement in heart wall motion or function. - The
system 10 may also be used in association with other diagnostic or therapeutic modalities to achieve regional systemic therapy. For example, a first selected treatment modality can be applied to the body to achieve a desired systemic effect (for example, the restriction of blood flow). A second selected treatment modality, which comprises the audible acousticenergy delivery system 10 previously described, can also be applied before, during, or after the first treatment modality, at least for a period of time, to transcutaneously apply acoustic energy to a selected localized region of the body (e.g., the thoracic cavity) to achieve a different, and perhaps opposite, localized system result, e.g., increased tissue perfusion. - For example, an individual who has received a drug that systemically decreases blood flow or blood pressure may experience a need for increased blood perfusion to the heart, e.g., upon experiencing a heart attack. In this situation, the audible acoustic
energy delivery system 10 can be used to locally apply audible acoustic energy to the thoracic cavity, to thereby locally increase blood perfusion to and in the heart, while systematic blood perfusion remains otherwise lowered outside the region of the heart due to the presence of the drug in the circulatory system of the individual. - As another example, this demonstrating the ability of locally applied acoustic energy to increase drug uptake, a chemotherapy drug may be systemically or locally delivered (by injection or by catheter) to an individual. The audible acoustic
energy delivery system 10 can be used to locally supply audible acoustic energy to the targeted region, where the tumor is, to locally increase perfusion or uptake of the drug. - The purposeful design of the durable and disposable equipment of the
system 10 makes it possible to carry out these therapeutic protocols outside a traditional medical setting, such as in a person's home. - Various features of the invention are set forth in the following claims.
Claims (2)
1. A method for achieving regional systemic therapy in an individual comprising the steps of
administering an agent to the individual,
providing a system comprising an audible acoustic energy applicator sized to be placed in acoustic contact with the individual to transcutaneously apply audible acoustic energy to the targeted body region, and an electrical signal generating machine adapted to be coupled to the audible acoustic energy applicator, the electrical signal generating machine including a controller to generate electrical signals to operate the audible acoustic energy applicator during a treatment session to produce audible acoustic energy, and
operating the system to apply audible acoustic energy to a targeted body region to cause vasodilation and/or increase tissue perfusion to affect an increase in uptake of the agent in the targeted, body region before, during or after administration of the agent to the individual.
2. A method according to claim 1
wherein the agent in an angiogenic material.
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US11/811,373 US20070244415A1 (en) | 2003-02-05 | 2007-06-08 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
US12/589,740 US20100049100A1 (en) | 2002-07-24 | 2009-10-28 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US10/359,040 US7229423B2 (en) | 2003-02-05 | 2003-02-05 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
US11/811,373 US20070244415A1 (en) | 2003-02-05 | 2007-06-08 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
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US10/359,040 Division US7229423B2 (en) | 2002-07-24 | 2003-02-05 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
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US12/589,740 Abandoned US20100049100A1 (en) | 2002-07-24 | 2009-10-28 | Systems and methods for applying audible acoustic energy to increase tissue perfusion and/or vasodilation |
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US8382672B2 (en) | 2010-03-12 | 2013-02-26 | Claire Andrews | Macro/micro duty cycle devices, systems, and methods employing low-frequency ultrasound or other cyclical pressure energies |
US8585597B2 (en) | 2010-03-12 | 2013-11-19 | Sonogenix, Inc. | Renal injury inhibiting devices, systems, and methods employing low-frequency ultrasound or other cyclical pressure energies |
US9420990B2 (en) | 2010-03-12 | 2016-08-23 | The Regents Of The University Of California | Renal injury inhibiting devices, systems, and methods employing low-frequency ultrasound or other cyclical pressure energies |
US10328287B2 (en) | 2010-03-12 | 2019-06-25 | The Regents Of The University Of California | Renal injury inhibiting devices, systems, and methods employing low-frequency ultrasound or other cyclical pressure energies |
Also Published As
Publication number | Publication date |
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US7229423B2 (en) | 2007-06-12 |
US20100049100A1 (en) | 2010-02-25 |
US20040153009A1 (en) | 2004-08-05 |
WO2004071570A3 (en) | 2006-08-17 |
WO2004071570A2 (en) | 2004-08-26 |
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