Abstract:
A method for measuring frequency response is provided that includes supplying ultrasonic energy to an ultrasonic device configured to impart energy to tissue, providing a drive signal and a noise signal, combining the drive signal and the noise signal to create a combined signal, amplifying the combined signal and providing the amplified signal to the ultrasonic device, receiving an output signal from the ultrasonic device and the noise signal, calculating a transfer function estimate based on the output signal and the noise signal, adjusting the drive signal generator based on the calculated transfer function estimate, and determining a phase difference by time aligning the noise signal in the output signal with the noise signal provided.

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
       [0001]    The present application is a continuation application of U.S. patent application Ser. No. 13/400,350, filed on Feb. 20, 2012, which is a continuation application of U.S. patent application Ser. No. 12/561,067, now U.S. Pat. No. 8,207,652, filed on Sep. 16, 2009, the entire contents of which are incorporated by reference herein. 
     
    
     BACKGROUND 
       [0002]    1. Technical Field 
         [0003]    The present disclosure relates to an ultrasonic surgical system. More particularly, but not exclusively, it relates to an ultrasonic surgical system able to achieve precise control of a desired operating point. 
         [0004]    2. Background of Related Art 
         [0005]    Devices which effectively utilize ultrasonic energy for a variety of applications are well-known in a number of diverse arts. A laparoscopic tool where the surgeon may use a scissors-type, a pistol or trigger type grip outside the body to operate a manipulative, gripping or clamping mechanism at a distal end of the tool within the body is useful for use with ultrasonically operated haemostatic cutting tools. Such haemostatic cutting tools are known from British Patent Number 2333709B, International Patent Applications Numbers PCT/GB99/00162 and PCT/GBOO/01580, and U.S. Pat. No. 5,322,055. 
         [0006]    Each of the above identified patents and patent applications describes a surgical tool comprising means to generate ultrasonic vibrations and a waveguide, operatively connected at a proximal end to said generating means, and provided at a distal end with cutting and/or coagulating means. Each tool is provided with a jaw to hold tissue to be treated in contact with the ultrasonically vibrating cutting and/or coagulating means. 
         [0007]    The Ampulla (Gaussian) profile was published by Kleesattel (as early as 1962), and is employed as a basis for many ultrasonic devices in surgical applications including devices patented and commercialized by Cavitron and Valleylab (patents by Wuchinich, et al., 1977, Stoddard, et al., 2001) for use in ultrasonic aspiration. The Gaussian profile is used in practice to establish and control the resonance and mechanical gain of devices. A resonator, a connecting body and the device act together as a three-body system to provide a mechanical gain, which is defined as the ratio of output stroke amplitude of the radiating tip to the input amplitude of the resonator. The mechanical gain is the result of the strain induced in the materials of which the resonator, the connecting body and the ultrasonic device are composed. 
         [0008]    The magnetostrictive transducer coupled with the connecting body functions as the first stage of the booster device with a mechanical gain of about 2:1, due to the reduction in area ratio of the wall of the complex geometry. The major diameter of the device transitions to the large diameter of the Gaussian in a stepped device geometry with a gain of as large as about 5:1, again due to reduction in area ratio. The mechanical gain increases in the Gaussian due to the Square Root of (1+2*Ln (Area Ratio)), where Ln is the natural logarithm, or about 2:1 for the devices of interest. The total mechanical gain is the product of these constituents, or as large as 20:1 for this example. Thus, the application of ultrasonically vibrating surgical devices used to fragment and remove unwanted tissue with significant precision and safety has led to the development of a number of valuable surgical procedures. Accordingly, the use of ultrasonic aspirators for the fragmentation and surgical removal of tissue from a body has become known. Initially, the technique of surgical aspiration was applied for the fragmentation and removal of cataract tissue. Later, such techniques were applied with significant success to neurosurgery and other surgical specialties where the application of ultrasonic technology through a handheld device for selectively removing tissue on a layer-by-layer basis with precise control has proven feasible. 
         [0009]    Certain devices known in the art characteristically produce continuous vibrations having substantially constant amplitude at a predetermined frequency (i.e. 20-30 kHz). Certain limitations have emerged in attempts to use such devices in a broad spectrum of surgical procedures. For example, the action of a continuously vibrating tip may not have a desired effect in breaking up certain types of body tissue, bone, etc. Because the ultrasonic frequency is limited by the physical characteristics of the handheld device, only the motion available at the tip provides the needed motion to break up a particular tissue. All interaction with the tissue is at the tip, some being purely mechanical and some being ultrasonic. The devices may have limitations in fragmenting some tissues. The limited focus of such a device may render it ineffective for certain applications due to the vibrations which may be provided by the handheld device. For certain medical procedures, it may be necessary to use multiple hand held devices or it may be necessary to use the same console for powering different handheld devices. 
         [0010]    Certain devices known in the art characteristically produce continuous vibrations having a substantially constant amplitude at a frequency of about twenty to about thirty kHz up to about forty to about fifty kHz. The amplitude is inversely proportional to frequency and directly proportional to wavelength because the higher frequency transducers generally have less powerful resonators. For example, U.S. Pat. Nos. 4,063,557, 4,223,676 and 4,425,115 disclose devices suitable for the removal of soft tissue which are particularly adapted for removing highly compliant elastic tissue mixed with blood. Such devices are adapted to be continuously operated when the surgeon wishes to fragment and remove tissue. 
         [0011]    A known instrument for the ultrasonic fragmentation of tissue at an operation site and aspiration of the tissue particles and fluid away from the site is the CUSA™ 200 System Ultrasonic Aspirator; see also U.S. Pat. No. 4,827,911, now sold as the CUSA Excel™. When the longitudinally vibrating tip in such an aspirator is brought into contact with tissue, it gently, selectively and precisely fragments and removes the tissue. Depending on the reserve power of the transducer, the CUSA transducer amplitude can be adjusted independently of the frequency. In simple harmonic motion devices, the frequency is independent of amplitude. Advantages of this unique surgical instrument include minimal damage to healthy tissue in a tumor removal procedure, skeletoning of blood vessels, prompt healing of tissue, minimal heating or tearing of margins of surrounding tissue, minimal pulling of healthy tissue, and excellent tactile feedback for selectively controlled tissue fragmentation and removal. 
         [0012]    In many surgical procedures where ultrasonic fragmentation instruments are employed, additional instruments are required for tissue cutting and hemostasis at the operation site. For example, hemostasis is needed in desiccation techniques for deep coagulation to dry out large volumes of tissue and also in fulguration techniques for spray coagulation to dry out the surface of tissues. 
         [0013]    The apparatus disclosed in U.S. Pat. Nos. 4,931,047 and 5,015,227 provide hemostasis in combination with an ultrasonically vibrating surgical fragmentation instrument and aspirator. The apparatus effectively provide both a coagulation capability and an enhanced ability to fragment and aspirate tissue in a manner which reduces trauma to surrounding tissue. 
         [0014]    U.S. Pat. No. 4,750,488 and its two continuation Patents, U.S. Pat. Nos. 4,750,901 and 4,922,902, disclose methods and apparatus which utilize a combination of ultrasonic fragmentation, aspiration and cauterization. 
         [0015]    In U.S. Pat. no. 5,462,522, there is disclosed, an ultrasonic therapeutic apparatus. The apparatus includes a water supply unit for supplying cooling water to cool the probe; a suction unit for removing waste matter by suction from the organic tissue treated by means of the cooling water and the probe; an ultrasonic output setting section for setting a preset value for an ultrasonic output from the ultrasonic vibrator; a feedwater output setting section for setting a preset value for a feedwater output from the water supply unit; and a feedwater output control section for controlling the feedwater output setting by the feedwater output setting section so that the preset feedwater output value is a value such that the probe is cooled and is not excessively heated. 
         [0016]    In U.S. Published Application 2009/0143805 A1, there is disclosed, cutting instruments that utilize ultrasonic waves generate vibrations with an ultrasonic transducer along a longitudinal axis of a cutting blade. By placing a resonant wave along the length of the blade, high-speed longitudinal mechanical movement is produced at the end of the blade. These instruments are advantageous because the mechanical vibrations transmitted to the end of the blade are very effective at cutting organic tissue and, simultaneously, coagulate the tissue using the heat energy produced by the ultrasonic frequencies. Such instruments are particularly well suited for use in minimally invasive procedures, such as endoscopic or laparoscopic procedures, where the blade is passed through a trocar to reach the surgical site. 
         [0017]    In an apparatus which fragments, cuts or coagulate tissue by the ultrasonic vibration of a tool tip, it is desirable, for optimum efficiency and energy utilization, that the transducer which provides the ultrasonic vibration operate at resonant frequency. The transducer design establishes the resonant frequency of the system, while the generator tracks the resonant frequency. The generator produces the electrical driving signal to vibrate the transducer at resonant frequency. However, changes in operational parameters, such as, changes in temperature, thermal expansion and load impedance, result in deviations in the resonant frequency. 
         [0018]    More specifically, as the temperature increases, the material density decreases and the speed of sound increases. The increase in temperature may lead to a lower equivalent mass of the key system components, especially the device which has a very low mass and can heat up and cool down quickly. The lower equivalent mass may lead to a change in equivalent resonant frequency. Additionally, when the water supply unit supplies water to cool down the device, the water adds mass to the device as well as acting as a coolant to maintain the temperature of the device. As such, the presence of water may change the equivalent resonant frequency. 
       SUMMARY 
       [0019]    The present disclosure relates to an ultrasonic system that includes an ultrasonic device configured to impart ultrasonic energy to tissue. The system also includes an ultrasonic generator configured to supply power to the ultrasonic device. The ultrasonic generator has a controllable drive signal generator as part of a negative feedback loop configured to provide a drive signal, a controllable noise signal generator configure to provide a noise signal, and a controller. The controller receives an output signal from the ultrasonic device and the noise signal from the noise signal generator, calculates a transfer function estimate based on the output signal and the noise signal, and adjusts the drive signal generator based on the calculated transfer function estimate. 
         [0020]    In another embodiment according to the present disclosure, an ultrasonic generator configured to supply power to an ultrasonic device is provided. The ultrasonic generator has a drive signal generator configured to provide a drive signal, a noise signal generator configured to provide a noise signal, and an adder configured to combine the drive signal and the noise signal. The ultrasonic generator also includes an amplifier having a gain configured to amplify the combined signal. A controller is configured to receive an output signal from the ultrasonic device and the noise signal from the noise signal generator, calculate a transfer function estimate based on the output signal, the noise signal and the gain, and adjust the drive signal generator based on the calculated transfer function estimate. 
         [0021]    In yet another embodiment according to the present disclosure, an ultrasonic generator configured to supply power to an ultrasonic device is provided. The ultrasonic generator has a drive signal generator configured to provide a drive signal, an amplifier having a gain configured to amplify the drive signal, a noise signal generator configured to provide a noise signal, and a resonance circuit configured to provide an output to the resonator of the ultrasonic device. The ultrasonic generator also includes a transformer having a first primary winding coupled to the amplifier, a second primary winding coupled to the noise signal generator and a secondary winding coupled to the resonance circuit. A controller is also provided that is configured to receive an output signal from the ultrasonic device and the noise signal from the noise signal generator, calculate a transfer function estimate based on the output signal and the noise signal, and adjust the drive signal generator based on the calculated transfer function estimate. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0022]    The above and other aspects, features, and advantages of the present disclosure will become more apparent in light of the following detailed description when taken in conjunction with the accompanying drawings in which: 
           [0023]      FIG. 1  is a perspective view of an ultrasonic device in accordance with an embodiment of the present disclosure; 
           [0024]      FIG. 2  is a cross-sectional view of a part of the handset of the tool of  FIG. 1  including a turning element; 
           [0025]      FIG. 3  is a perspective view of an ultrasonic device in accordance with an embodiment of the present disclosure; 
           [0026]      FIG. 4  is an enlarged view of a tip of the ultrasonic device of  FIG. 3 ; 
           [0027]      FIG. 5  is a top view of the ultrasonic device of  FIG. 3  with a channel shown in phantom; 
           [0028]      FIG. 6  is a side view of the ultrasonic device of  FIG. 3 ; 
           [0029]      FIG. 7  is a cross-sectional view of the ultrasonic surgical device of  FIG. 5 ; 
           [0030]      FIG. 8  is a cross-sectional view of the ultrasonic surgical device of  FIG. 6 ; 
           [0031]      FIG. 9  is a side elevational view of an exemplary handle with the left-side shell removed in accordance with an embodiment of the present disclosure; 
           [0032]      FIG. 10  is a perspective view from the front left side of a hand-held ultrasonic cutting pen device in accordance with an embodiment of the present disclosure; 
           [0033]      FIG. 11  is a side elevational view of the hand-held ultrasonic cutting pen device of  FIG. 10  from the left side; 
           [0034]      FIG. 12  is a side elevational view of the hand-held ultrasonic cutting pen device of  FIG. 11  with the left-side shell removed; 
           [0035]      FIG. 13  is a diagrammatic illustration of a hand-held ultrasonic cutting pen device to be connected to a man-portable, control and power supply assembly in accordance with an embodiment of the present disclosure; 
           [0036]      FIG. 14  is a perspective view of a hand-held ultrasonic cutting pen device to be connected to a man-portable, control and power supply assembly in accordance with an embodiment of the present disclosure; 
           [0037]      FIG. 15  is a perspective view of the hand-held ultrasonic cutting pen device of  FIG. 15  with a left-half shell removed; 
           [0038]      FIG. 16  is a perspective view of a portable, control and power supply assembly to be connected to a hand-held ultrasonic cutting pen device in accordance with an embodiment of the present disclosure; 
           [0039]      FIG. 17  is a schematic of an ultrasonic generator in accordance with an embodiment of the present disclosure; and 
           [0040]      FIG. 18  is a schematic of an ultrasonic generator in accordance with an embodiment of the present disclosure. 
       
    
    
     DETAILED DESCRIPTION 
       [0041]    Particular embodiments of the present disclosure will be described hereinbelow with reference to the accompanying drawings; however, it is to be understood that the disclosed embodiments are merely exemplary of the disclosure, which may be embodied in various forms. Well-known functions or constructions are not described in detail to avoid obscuring the present disclosure in unnecessary detail. Therefore, specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims and as a representative basis for teaching one skilled in the art to variously employ the present disclosure in virtually any appropriately detailed structure. 
         [0042]    Embodiments of the presently disclosed ultrasonic surgical system are described in detail with reference to the drawings, in which like reference numerals designate identical or corresponding elements in each of the several views. As used herein, the term “distal” refers to that portion of the instrument, or component thereof which is further from the user while the term “proximal” refers to that portion of the instrument or component thereof which is closer to the user. 
         [0043]    Referring now to the drawings and to  FIG. 1  in particular, a surgical tool, in this case an ultrasonic surgical haemostatic tool, comprises an elongate waveguide  1  for ultrasonic vibrations (torsional mode ultrasonic vibrations are preferred, although longitudinal mode ultrasonic vibrations may also be utilized). An example of such an ultrasonic surgical device is disclosed in U.S. Pat. No. 7,520,865 to Young et al. currently owned by and assigned to Covidien AG, the entire contents of which are incorporated herein by reference. The waveguide  1  defines a longitudinal axis of the tool, as shown by dotted line  2 - 2 . A proximal end  1   a  of the waveguide  1  is mounted to an ultrasonic vibration generator  20  which will be described in more detail hereinbelow. 
         [0044]    The waveguide  1  is disposed coaxially within an elongate carrier tube  3 , which is mounted at its proximal end to a cylindrical turning element  4 . The carrier tube  3  and the turning element  4  are rotatable as a unit about the longitudinal axis  2 , in the sense of arrows  5 . The turning element  4  is acted on by a trigger mechanism or other manual operating means, as detailed below. A jaw member  6  is mounted pivotably to a distal end  3   b  of the carrier tube  3 . 
         [0045]    A plurality of spacers (not shown) may be provided between the waveguide  1  and an inner wall of the carrier tube  3 , insulating the carrier tube  3  from ultrasonic vibrations transmitted by the waveguide  1  and maintaining their relative disposition. 
         [0046]    An outer tube  7  is disposed coaxially around the carrier tube  3  and the waveguide  1 . The outer tube  7  is mounted at its proximal end to a mounting block  8 , which is mounted non-rotatably to a handset of the tool (not shown in this Figure). At its distal end, the outer tube  7  is provided with a guide lobe  9 , which bears on a rearward facing contact surface  10  of the jaw member  6 . The turning element  4  and the mounting block  8  are biased apart, for example with a spring, other resilient device, or cam means such that the guide lobe  9  and the contact surface  10  remain co-operatingly in contact one with another. 
         [0047]    When the carrier tube  3  is rotated, the contact surface  10  of the jaw member  6  mounted thereto moves across the guide lobe  9  of the stationary outer tube  7 , thereby causing a pivoting movement of the jaw member  6  away from or towards contact with the distal end  16  of the waveguide  1 , as detailed below. 
         [0048]    The outer tube  7  also acts as a protective sheath for the greater part of the rotatable carrier tube  3  and the waveguide  1 , for example protecting them from body fluids as far as possible. In a preferred embodiment of the tool, the carrier tube  3  and the outer tube  7  are detachable from the handset of the tool. The carrier tube  3  and the jaw member  6  that it carries may then be withdrawn in a distal direction from the outer tube  7 , so that each may be cleaned and sterilized separately before re-use, or alternatively so that either or both may be disposed of and replaced with a fresh equivalent. 
         [0049]      FIG. 2  shows a part of the handset of the tool, together with proximal portions of the outer tube  7  and the carrier tube  3 . The mounting block  8  is mounted, permanently or removably, to a handset casing  11 . In this particular embodiment of the tool, the turning element  4  is provided with a part helical slot  12  in its cylindrical wall, which is adapted to receive a driving stud (not shown) mounted to a trigger mechanism (not shown) which extends out of the casing  11  through an aperture  13  provided therefor. The trigger mechanism may optionally be mounted to a pivot mounting  14  on the casing  11 , as shown, or to a pivot mounting disposed adjacent the aperture  13 . Pivoting movement of the trigger mechanism, which is configured to be grasped by a hand of a user, moves the driving stud in a generally longitudinal direction. As the driving stud is constrained to move within the part helical slot  12 , a forward motion of the stud causes the turning element  4 , and hence the carrier tube  3 , to rotate in an anticlockwise sense (viewed from a proximal end of the tool) and a rearward motion of the stud causes the turning element  4  and the carrier tube  3  to rotate in a clockwise sense. 
         [0050]    The ultrasonic vibration generator is conveniently mounted inside a detachable element of the casing  11 .  FIG. 2  shows the handset with that element detached, and the waveguide  1 , mounted to the ultrasonic generator, thereby withdrawn from its operating disposition disposed coaxially within the carrier tube  3 . 
         [0051]    An ultrasonic device  100 , in accordance with one embodiment of the present disclosure, is illustrated in  FIG. 3 . Ultrasonic device  100  is adapted for use in an ultrasonic surgical system having an ultrasonic handpiece. An example of such an ultrasonic surgical system is disclosed in U.S. Pat. No. 6,214,017 to Stoddard et al. currently owned by and assigned to Sherwood Services AG, the entire contents of which are incorporated herein by reference. Alternatively, ultrasonic device  100  may be adapted for use with the ultrasonic surgical system disclosed in U.S. Pat. No. 4,063,557 to Wuchinich et al., the entire contents of which are incorporated herein by reference. 
         [0052]    Referring to  FIGS. 3 and 4 , in one embodiment of the present disclosure, ultrasonic device  100  includes an adapter  130  having a first or proximal end  172  and a second or distal end  174 . Extending from proximal end  172 , adapter  130  includes a fillet  132 , a nut  134  and a flange  136  terminating at distal end  174 . Flange  136  includes a leading edge  138 . Proximal end  172  of adapter  130  is configured to connect ultrasonic device  100  to an ultrasonic handpiece or resonator  150  via a connecting portion  140 . Connecting portion  140  is capable of coupling ultrasonic device  100  and connecting portion  140  to ultrasonic handpiece or resonator  150 . As used herein, the term “resonator” is used to refer to what is often referred to in the literature as an ultrasonic handpiece. Ultrasonic device  100  includes an elongated member  110  having a first or proximal end which coincides with distal end  174  of adapter  130 . Elongated member  110  has a second or distal end  180 , and distal end  174  of adapter  130  is joined, in one embodiment unitarily, to the coinciding proximal end of elongated member  110 . Distal end  180  of elongated member  110  is configured as a tip lead  120 . Tip lead  120  extends from a first or proximal end, as is discussed in more detail below. 
         [0053]    Connecting portion  140  includes a first or proximal end  142  which is configured to connect to a resonator  150  at a distal end thereof. Resonator  150  includes, in one embodiment, a magnetostrictive transducer, although other transducer types can be included such as a piezoelectric transducer. Resonator  150  is supplied power from ultrasonic generator  200  (described in more detail below) such that resonator  150  operates at a desired frequency. In one embodiment, ultrasonic device  100  is made of titanium, although other materials such as stainless steel can be used. 
         [0054]    As seen in  FIG. 5 , an internal channel  160  is formed within elongated member  110 . As is known in the art, the channel terminates in the connecting body, and does not continue in the resonator. The resonator is typically a laminated core-stack of Permanickel. In most implementations, the central channel supports aspiration suction of tissue. The channel also affords greater mechanical gain because the gain is dependent on the reduction in area ratio of the thin walls. The primary purpose of the channel is to support gain for bone tips with the chisel/awl distal ends. The internal channels of the bone abrading tips in the disclosure shown and described below would also aid in cooling, where irrigation liquid is suctioned via the internal diameter channel. Surgical procedures on bone typically employ an auxiliary suction tube to remove the larger volumes of irrigation liquid and bone debris. 
         [0055]    Referring to  FIGS. 5-6 ,  FIG. 8  is a top view of ultrasonic device  100  of  FIG. 3  with channel  160  shown in phantom formed within elongated member  110 .  FIG. 6  is a side view of ultrasonic device  100  of  FIG. 3  with channel  160  in phantom formed within elongated member  110 .  FIG. 7  is a cross-sectional view of ultrasonic surgical device  100  of  FIG. 5  showing channel  160  formed within elongated member  110 .  FIG. 8  is a cross-sectional view of ultrasonic surgical device  100  of  FIG. 6  again showing channel  160  formed within elongated member  110 . Internal channel  160  is formed within adapter  130  and elongated member  110  of ultrasonic device  100 . 
         [0056]    Elongated member  110  is tapered such that the cross-sectional area is a maximum at proximal end  174  interfacing with adapter  130  and is a minimum at proximal end  178  of tip lead  120 . Channel  160  is a substantially constant diameter central hole of diameter d 1  formed within elongated member  110  to enable enhanced mechanical gain in device  100 . In the case of a device with a channel, it is the area ratio of the cross-sectional area based on the outer diameter of the elongated member  110  near the leading edge  138  of flange  136  versus the cross-sectional area based on the outer diameter of the elongated member  110  at the distal end  176 . The area ratio along the length L of the device is decreased towards tip lead  120  at the distal end of elongated member  110 , and velocity and elongation of the titanium particles are increased. The ultrasonic wave is supported by particle motion in the titanium. The particles vibrate about their neutral position in a longitudinal or extensional wave. The particles do not move along the length of the device, but only vibrate, just as a cork or bobber shows that a wave passes through water via the liquid. As the device wall thickness decreases, more strain occurs in the metal as the particles move a greater distance about their neutral position. The displacement of the end of the device is due to strain along the device. All the particles supporting the wave are moving at the same resonant frequency. The greater the strain, the greater the velocity of the particles necessary to maintain the same frequency. 
         [0057]    As best illustrated in  FIG. 4 , distal end  180  of tip lead  120  has a semi-circular planar surface configuration  122 , such that distal end  180  of ultrasonic device  100  is in the form of a chisel and an awl. (Awls are utilized in manual boring of holes, such as in boring leather, or wood). Tip  180  of ultrasonic device  100  is blunt or dull. The boring of holes with device  100  is better facilitated with slightly semi-circular manual motion; however plunge cuts in bone and wood have been accomplished with just longitudinal motion of device  100 . The combination of the chisel and awl distal end  180  of device  100  supports defined cutting or abrasion of sections, planes, notches, grooves, and holes in bone. Channel or central hole  160  extends from proximal end  172  of adapter  130  to approximately distal end  176  which coincides with proximal end of solid portion  114  of elongated member  110 . 
         [0058]    Another example of an ultrasonic surgical device is disclosed in United States Published Application Number 20090143805 to Palmer et al. currently owned by and assigned to Syntheon, LLC, the entire contents of which are incorporated herein by reference. Referring now to  FIG. 9 , an ultrasonic surgical device  900  in accordance with an embodiment of the present disclosure is depicted. When an ultrasonic-movement-generation assembly  902  is coupled to a handle  914 , the transducer  916  is caused to be realeasably physically coupled to a waveguide  904 ,  908  through the transducer attachment port  918  and waveguide attachment port  920 . It is envisioned that the transducer assembly  916  can be temporarily locked into a fixed rotational position so that the waveguide  904  can be attached to the threads (not shown) with sufficient force. This physical coupling between the waveguide  904  and the transducer assembly  916  allows the transducer assembly  916  to impart movement to the waveguide  904  when power is applied to the transducer assembly  916 . 
         [0059]    The device  900  has a spindle  906  that attaches to the waveguide  908 . The spindle  906  has indentions that allow a surgeon to easily rotate the spindle  906  and, therefore, the attached waveguide  908  and transducer assembly  916  that is attached to the waveguide  908 . Such a configuration is useful for obtaining the proper cutting-blade angle during surgery. To provide for this rotation, in one embodiment, the transducer assembly  916  is able to rotate freely within the transducer housing  910 . 
         [0060]    During initial coupling of the transducer assembly  916  and waveguide  904 , all that is needed is that one of the transducer assembly  916  and the waveguide  904  remains relatively stationary with respect to the other. According to one embodiment of the present disclosure, when the transducer assembly  916  is located inside the housing  910  where it cannot be readily secured by the operator, for example, by holding it steady by hand when the waveguide  908  is being secured--the ultrasonic-movement-generation assembly  902  is provided with a button (not shown) that slides into a recess in the housing  910  or, alternatively, by fixing the rotation of the transducer assembly  916  at a maximum rotational angle so that, once the maximum rotation is reached, for example,  360  degrees of rotation, no additional rotation is possible and the waveguide  904  can be screwed thereon. A maximum rotation in the opposite direction will allow the waveguide  904  to be removed as well. 
         [0061]    In an alternative exemplary embodiment to the gun device,  FIGS. 10 to 12  illustrate an entirely hand-held and fully self-contained cautery and cutting device  1000 . This cutting device  1000  reduces the size of the power supply  1002  considerably. Here, in comparison to the previous embodiments, the waveguide  1004  is reduced in length. The ultrasonic generator and the power supply  1002  reside at the handpiece  1010 . As in the other embodiments described above, the pen shaped device shown in  FIGS. 10 to 12  could have, in accordance with one embodiment, a sealed body  1002 , where the body  1002  housing the ultrasonic generator and the power supply  1002  is autoclavable and the waveguide  1004  is simply replaced for each procedure. 
         [0062]      FIG. 13  depicts another shape for the cautery/cutting device  1300  that is shaped to fit into a surgeon&#39;s hand for ease of use. Another shape for the pen device  1500  is shown in  FIGS. 14 and 15  and is similar to a writing pen so that the surgery can be carried out with the device  1500  to approximate writing—a process that is comfortable to most physicians. The pen  1300 ,  1500  includes all of the transducer components—the transducer  1302 ,  1502 , the protective cannula  1304 ,  1504 , and the waveguide  1306 ,  1506 . 
         [0063]    In these embodiments, the base  1600 , shown in  FIG. 16 , has a body  1606  that houses a self-contained power source (i.e., a battery) and a generator circuit operable to generate an output waveform and is sized to be handheld. The base  1600  is connected through a communications and power tether cord  1602 , illustrated diagrammatically in the figures with a dashed line, to the pen-shaped ultrasonic waveguide handle  1500 , shown in  FIGS. 15-16 . When in operation, the transducer  1502  within the handle  1500  is driven by a plurality of driving waves output from the waveform generator within the body  1506 . 
         [0064]    The base  1600  has a user interface  1604  that can be used to communicate data and carry out functions of the device, such as testing and operation. Through the user interface  1604 , the device can be tested in the sealed package without even opening the package. For instance, in one embodiment, a user can press one or more non-illustrated buttons (physical or electronic) in a given sequence (e.g., 5 times in a row) and, thereby, cause the user interface  1604  to display a status of the battery and/or a status of the logic circuitry, all without having to remove it from the sealed package. This is helpful in case of a defect, such as a bad battery, as the purchaser would be able to return the device to the manufacturer before use and, thereby, prove non-use of the device to receive credit. In this embodiment, all of the ultrasonic generator components reside in the base  1600 . 
         [0065]    The base  1600  is also provided with a non-illustrated clothing attachment mechanism that can be a simple belt clip, or any other way of attaching a device to a wearer. The clothing attachment mechanism allows a surgeon or nurse to wear the base  1600  during a surgery so that the cord  1602  will always be of sufficient length, i.e., as long as his arm can reach, no matter where the surgeon is standing. 
         [0066]    Referring to  FIG. 17 , an apparatus or ultrasonic generator  1700  is provided which is configured to supply power to the resonator  150 . Ultrasonic generator  1700  uses a negative feedback loop to control the output of the ultrasonic generator  1700 . Ultrasonic generator  1700  includes a controllable drive signal generator  1702  that generates a drive signal (A ds ) to control the ultrasonic device. The drive signal generator  1702  outputs a sine wave in an embodiment of the present disclosure. The sine wave may also be substituted with a square wave, triangular wave or a pulse width modulated (PWM) form of the sine wave. Noise generator  1704  is also provided which outputs a controllable noise signal (A ns ). The ultrasonic device tends to self heat which would increase resonance. Alternatively, the added load at the distal tip of the device will add mass and/or compliance, which will also change the resonance. The resonance changes quickly as the ultrasonic device cools again or is transiently loaded and unloaded. By adding a noise signal such as a “pink” noise or narrowband white noise, with many Fast Fourier Transform (FFT) bins averaged together, an operating point can be determined and the ultrasonic device could be tuned to the operating point. A FFT is an efficient algorithm to compute the discrete Fourier transform (DFT) and its inverse. A DFT decomposes a sequence of values into components of different frequencies. This operation is useful in many fields but computing it directly from the definition is often too slow to be practical. An FFT is a way to compute the same result more quickly: computing a DFT of N points in the obvious way, using the definition, takes O(N  2 ) arithmetical operations, while an FFT can compute the same result in only O(N log N) operations. The difference in speed can be substantial, especially for long data sets where N may be in the thousands or millions—in practice, the computation time can be reduced by several orders of magnitude in such cases, and the improvement is roughly proportional to N/log(N) 
         [0067]    In another embodiment of the present disclosure, a pseudo random noise sequence (PRNS) may be provided as a noise signal by noise signal generator  1704 . Using a PRNS noise signal allows the ultrasonic system to determine the phase of an output signal with respect to the input signal. 
         [0068]    The drive signal and noise signal are combined (A dns ) by adder  1706  and the combined signal is provided to amplifier  1708 . Amplifier  1708  has a gain “k” which can be a predetermined value set by the manufacturer or could be adjusted by a user of the ultrasonic system. The output of amplifier  1708  is provided to the ultrasonic device  100  as described above. Ultrasonic device has a transfer function “G” that determines the resonance and electro-mechanical gain of the device as described above. Ultrasonic device outputs an ultrasonic signal (A out ) proportional to the stroke or mechanical force produced by the ultrasonic device that is to be controlled by the negative feedback loop. 
         [0069]    As shown in  FIG. 17 , the ultrasonic signal is provided to a controller  1710 . Controller  1710  also receives or has a priori information on the statistics of the noise signal from noise signal generator  1704 , the drive signal from drive signal generator  1702 , and the gain “k” from amplifier  1708 . Controller  1710  may be any available processor or logic circuit configured to perform the functions described below. Controller  1710  may also include a memory configured to store predetermined or measured parameters to use in the controller&#39;s  1710  operations. Although not shown, controller  1710  may be coupled to an input device, such as a keypad, keyboard, mouse, touch screen, scanner, or the like. Controller  1710  may also be coupled to an output device such as any type of display that provides a visual indication such as a monitor, light emitting diode display, liquid crystal display, printer, or the like. 
         [0070]    Because the increase in temperature may lead to a lower equivalent mass of the key ultrasonic system components (for instance, in one embodiment, the water supply unit supplies water to cool down the device where the water adds mass to the device as well as acting as a coolant to maintain the temperature of the device), the equivalent resonant frequency of the ultrasonic device may change. Accordingly, controller  1710  applies a transfer function using the FFT&#39;s of the ultrasonic signal output and the noise signal from noise signal generator  1704 . More specifically, the controller  1710  calculates the new transfer function estimate “Ĝ” of the ultrasonic device by dividing the average of the output power FFT&#39;s |A out | 2  by the input FFT&#39;s noise power |A ns | 2  and gain “k”. The controller  1710  can also determine the phase difference between the output power signal and the combined signal by time aligning the noise signal from noise signal generator  1704  and the noise signal in the output power signal. The phase difference may also be determined using a phase-locked loop (PLL) circuit (not shown). Based on the new transfer function estimate “Ĝ”, a new equivalent resonance frequency can be determined. Drive signal generator  1702  is adjusted by the controller  1710  to provide a new drive signal based on the new equivalent resonance frequency. 
         [0071]      FIG. 18  depicts another embodiment of an ultrasonic generator  1800  in accordance with the present disclosure. As shown in  FIG. 18 , a drive signal generator  1802  provides a drive signal to amplifier  1804 . Amplifier  1804  may be a non-linear amplifier such as Class D amplifier. A Class D amplifier is an electronic amplifier which, in contrast to the active resistance used in linear mode AB-class amplifiers, uses the switching mode of transistors to regulate power delivery. The amplifier, therefore, features high power efficiency (low energy losses), which additionally results in lower weight by eliminating bulky heat sinks. Additionally, if voltage conversion is necessary, the on-the-way high switching frequency allows the bulky audio transformers to be replaced by small inductors. Low pass 
         [0072]    LC-filtering smoothes the pulses out and restores the signal shape on the load. 
         [0073]    The output of amplifier  1804  is provided to an inductor L 1  which is coupled to a primary winding  1812  of a transformer  1810 . Unlike the embodiment described in  FIG. 17 , the ultrasonic generator  1800  provides a noise signal generator  1806  after the amplifier  1804 . The noise source is coupled to a winding on the primary side  1814  of transformer  1815 . The secondary winding of  1811  of transformer  1815  is coupled to primary winding  1812  of transformer  1810 . The secondary winding  1816  of transformer  1810  is coupled to an LC circuit or resonance circuit  1820  which then provides an output of both the drive signal and the noise signal to a resonator such as resonator  150  of ultrasonic device  100  described hereinabove. An LC circuit is a resonant circuit or tuned circuit that consists of an inductor, represented by the letter L, and a capacitor, represented by the letter C. When connected together, an electric current can alternate between them at the circuit&#39;s resonant frequency. The LC circuit is typically used to compensate for losses in the class D amplifier that may occur due to complex loading effects of the ultrasonic device. 
         [0074]    Similar to ultrasonic generator  1700 , the output of the ultrasonic device is provided to a controller  1830  which calculates the new transfer function estimate “Ĝ” of the ultrasonic device by dividing the average of the output power FFT&#39;s |A out | 2  by the input FFT&#39;s noise power |A ns | 2 . The controller  1830  can also determine the phase difference between the output power signal and the combined signal by “time aligning” the noise signal from noise signal generator  1806  and the noise signal in the output power signal. Based on the new transfer function estimate “Ĝ”, a new equivalent resonance frequency can be determined. Drive signal generator  1802  is adjusted by the controller  1830  to provide a new drive signal based on the new equivalent resonance frequency. 
         [0075]    The described embodiments of the present disclosure are intended to be illustrative rather than restrictive, and are not intended to represent every embodiment of the present disclosure. Various modifications and variations can be made without departing from the spirit or scope of the disclosure as set forth in the following claims both literally and in equivalents recognized in law.