JP5166559B2 - How to generate energy for use in ophthalmic surgery equipment - Google Patents

Description

  The present invention relates to the field of ophthalmic surgery, and in particular, to a method for operating the shape, arrangement, and duration of pulses of ultrasonic energy generated by an ultrasonic handpiece of a phacoemulsification surgical apparatus.

  The human eye functions to transmit light through an outer transparent part called the cornea and to visualize it by focusing the image on the retina with the lens. And the quality of the focused image depends on many factors, such as the size and shape of the eyeball, and the transparency of the cornea and lens. When the transparency of the lens decreases due to aging or illness, the light transmitted to the retina decreases, resulting in decreased visual acuity. Such defects in the lens of the eyeball are medically known as cataracts. A common treatment for this disease is to remove the lens by surgery and replace the function of the lens with an intraocular lens (IOL). In the United States, many of the cataractous lenses are removed by a surgical procedure called phacoemulsification. In this operation, a thin cutting tip or cutting needle is inserted into the diseased lens and vibrated ultrasonically. The vibrating cutting tip liquefies or emulsifies the lens so that the lens can be sucked out of the eyeball. Once removed, the diseased lens is replaced by an intraocular lens.

  Standard ultrasonic surgical equipment suitable for eye surgery includes an ultrasonically driven handpiece and an attached cutting tip and perfusion sleeve or other suitable perfusion equipment and electronic controller. And have. The handpiece assembly is attached to the electronic control device by an electric cable or connector and a flexible tube. The surgeon transmits the ultrasonic energy applied to the tissue and transmitted to the handpiece's mounted cutting tip by depressing the foot pedal to request the output set to the electronic controller up to the maximum output amount. Control the amount. On the other hand, the flexible tube supplies the perfusate to the eyeball through the handpiece assembly or pumps the suction liquid from the eyeball.

  The operating part of the handpiece is a hollow resonance bar or horn that is attached to the piezoelectric crystal and is centrally located. During phacoemulsification, the piezoelectric crystal is controlled by a controller and supplies the ultrasonic vibrations necessary to drive both the horn and the attached cutting tip. These piezoelectric crystal and horn assemblies are supported in the hollow body or shell of the handpiece by flexible mounting. Further, the distal end of the handpiece body terminates as a reduced diameter portion or a nose cone. The nosecone has an external thread for receiving a perfusion sleeve. Similarly, the distal end of the hole in the horn has an internal thread for receiving the external thread of the cutting tip. The perfusion sleeve also has a hole with an internal thread that is fastened to the external thread of the nose cone. The cutting tip is adjusted to project a predetermined amount beyond the open end of the perfusion sleeve.

  In use, the cutting tip and the distal end of the perfusion sleeve are inserted into a predetermined narrow incision in the cornea, sclera, or other portion. One known cutting tip is ultrasonically vibrated along the longitudinal axis within the perfusion sleeve by a piezoelectric crystal driven ultrasonic horn, thereby emulsifying the tissue at the selected site. The hollow cutting tip hole communicates with the horn hole and the suction tube from the handpiece to the electronic controller. Other suitable cutting tips have piezoelectric elements that create both longitudinal and torsional vibrations. One example of such a cutting tip is described in Patent Document 1, which is hereby incorporated herein by reference.

  A reduced pressure source or vacuum source in the electronic controller pumps or aspirates emulsified tissue from the eyeball into the collection device through the open distal end of the cutting tip, the cutting tip and horn hole, and a suction tube. The suction of emulsified tissue is facilitated by saline or other perfusate injected into the surgical site through a small annular gap between the inner surface of the perfusion sleeve and the cutting tip.

  One known surgical technique is to make the incision in the anterior chamber as small as possible to reduce the risk of induced astigmatism. These small incisions become very narrow wounds that press against the perfusion sleeve against the oscillating cutting tip. Friction between the perfusion sleeve and the vibrating cutting tip generates heat. The cooling effect of the aspirated perfusate flowing through the cutting tip reduces the risk that the cutting tip will overheat and burn the tissue.

  Some known surgical devices employ a “pulse mode” in which the amplitude of a fixed width pulse can be changed using a controller such as a foot pedal. Other known surgical devices have an “off” time after each pulse in a series of pulses of periodic fixed width and constant amplitude. The “off” time can be varied using the controller. Other known devices use pulses with an initial maximum power level followed by a lower power level. For example, Patent Document 2 describes a pulse that increases from zero to an initial maximum output level and then decreases to a lower output level.

  While known surgical devices have been used effectively, they can be improved by allowing better pulse control to be used in a variety of surgical instruments and applications. For example, known surgical devices that use square or rectangular pulses typically have power levels that increase very quickly to a maximum power level. Sharp pulse transitions reduce the ability to retain and emulsify the lens material. In particular, when the lens material is held at the tip of the ultrasonic handpiece by vacuum, a very fast (almost immediate) pulse ramp up to the maximum power level causes the lens material to move from the tip very quickly. Move or press away. This makes it difficult to cut the lens material. In other words, due to rapid power transitions, an imbalance occurs between the vacuum at the ultrasound tip that holds or aligns the lens material and the ability to emulsify the lens material.

  Other known devices operate at high power levels, even if low power or no power is sufficient. For example, for a rectangular pulse, an initial high power level may be required to provide power to emulsify the lens material. However, no further output is required after the lens material has been removed or emulsified. A rectangular pulse that applies the same amount of power after removal or emulsification of the lens material results in excessive heat being applied to the tissue and harming the patient.

  Furthermore, the pulse pattern used by some known surgical devices does not sufficiently reduce the cavitation effect. Cavitation consists of small bubbles resulting from the reciprocating motion of the ultrasonic tip. This movement creates a low pressure pocket and a high pressure pocket. When the ultrasonic tip moves backward, it causes a low pressure locally and the liquid evaporates, generating bubbles. The bubbles are compressed and abruptly contracted when the ultrasonic tip moves forward. The rapid shrinking of bubbles creates unnecessary heat and force, making surgery difficult and risking the patient.

US Pat. No. 6,402,769 International Application No. PCT / US2004 / 007318 US Pat. No. 3,589,363 U.S. Pat. No. 4,223,676 U.S. Pat. No. 4,246,902 US Pat. No. 4,493,694 U.S. Pat. No. 4,155,583 US Pat. No. 4,589,415 US Pat. No. 4,609,368 US Pat. No. 4,869,715 US Pat. No. 4,922,902 US Pat. No. 4,995,583 US Pat. No. 5,154,694 US Pat. No. 5,359,996 US Pat. No. 6,179,808 US Pat. No. 6,261,283

  Therefore, there continues to be a need for methods in which the pulse shape and duration can be manipulated for various phacoaspiration applications and operations.

  According to one embodiment of the present invention, a method for generating energy for use in an ophthalmic surgical instrument includes generating a pulse comprising an on time, a first off time, and a first amplitude. The first off time is longer than the on time. The method includes the steps of reducing a first off time of a pulse and increasing the amplitude of the pulse from a first amplitude to a second amplitude when the first off time is reduced to a predetermined second off time. Have.

  The first off time can be reduced in response to a controller such as a foot pedal. The first off time decreases until the foot pedal reaches a predetermined position corresponding to the pulse off time, after which the first off time becomes steady. The amplitude of the pulse increases after a predetermined second off time has become approximately the same as the on time depending on the foot pedal. The off time and amplitude can be adjusted by continuous movement of a single controller.

  According to another embodiment of the present invention, in a method for generating energy for use in an ophthalmic surgical instrument, generating a burst mode pulse and converting the burst mode pulse into a pulse mode pulse in accordance with the controller Process.

  According to yet another embodiment of the present invention, in a method for generating energy for use in an ophthalmic surgical instrument, generating a pulse mode pulse and converting the pulse mode pulse to a burst mode pulse in accordance with the controller And a step of causing

  The step of converting between the burst mode and the pulse mode is performed according to the movement of the foot pedal, and starts after the foot pedal reaches a predetermined position. The burst mode pulse is generated by generating a pulse having an on time, a first off time, and a first amplitude. The burst mode pulse is converted to a pulse mode pulse by reducing the first off time of the pulse to a second off time in response to the controller. When the second off time reaches a predetermined value, the amplitude of the pulse increases from the first amplitude to the second amplitude depending on the controller. The predetermined value may be the same as the on time or may be another desired value. The on-time is steady during the conversion process.

1 illustrates an exemplary phacoemulsification surgical device used in various embodiments. (A) shows a block diagram showing components of an exemplary phacoemulsification surgical apparatus, and (b) and (c) show pulses used in the phacoemulsification surgical apparatus. FIG. 6 illustrates a pulse with linear rise and decay components and a constant maximum amplitude component, according to one embodiment. FIG. 6 illustrates a pulse with a linear rise component and a linear decay component that meet at a maximum point according to another embodiment. FIG. 6 illustrates a combination of a pulse with a rectangular pulse and a pulse with a linear component, according to yet another embodiment. FIG. 6 illustrates a combination of a pulse with a rectangular pulse and a pulse with a linear component, according to yet another embodiment. FIG. 6 illustrates a combination of a pulse with a rectangular pulse and a pulse with a linear component, according to yet another embodiment. FIG. 6 illustrates a combination of a pulse with a rectangular pulse of the same amplitude and a pulse with a linear component according to yet another embodiment. FIG. 4 illustrates a pulse with a constant amplitude component with a linearly increasing component and a linearly decreasing component, with a continuously increasing output, according to one embodiment. FIG. 6 illustrates a pulse with a linear rise component and a linear decay component with an output that intersects at a maximum and continuously increases according to yet another embodiment. FIG. 6 illustrates a combination of a rectangular pulse with a continuously increasing output and a pulse having a linear component, according to one embodiment. FIG. 4 illustrates a pulse with a constant amplitude component with a linearly increasing component and a linearly decreasing component with a continuously decreasing output, according to one embodiment. FIG. 6 illustrates a pulse with a linearly rising component and a linearly decaying component that meet at a maximum point and with a continuously decreasing output, according to another embodiment. FIG. 6 illustrates a combination of a rectangular pulse with a continuously decreasing output and a pulse having a linear component, according to another embodiment. A known fixed burst mode pulse is shown. 1 shows a known linear burst mode pulse. A known pulse mode pulse is shown. FIG. 4 illustrates a continuous change from a burst mode pulse to a pulse mode pulse, depending on the controller, according to one embodiment. FIG. 6 illustrates a continuous change from a pulsed mode pulse to a burst mode pulse, depending on the controller, according to another embodiment. FIG. 6 illustrates a multi-segment rectangular pulse with two pulse segments with increasing amplitude, according to yet another embodiment. Fig. 5 shows a multi-segment rectangular pulse according to another embodiment comprising three pulse segments with increasing amplitude. 11 shows a packet of ultrasonic energy pulses shown in FIG. 14 shows a packet of pulses of ultrasonic energy shown in FIG.

  Referring now to the drawings wherein like reference numerals represent corresponding corresponding parts throughout the drawings.

  This specification describes an embodiment of a method for manipulating pulses of ultrasonic energy to control a surgical device used in, for example, phacoemulsification surgery. These embodiments are implemented by commercially available surgical devices or surgical control devices via appropriate hardware and software controls. 1 and 2 show an exemplary surgical device.

  FIG. 1 shows one suitable device and corresponds to the INFINITI® Vision System available from Alcon Laboratories at 76134 Fort Worth Q-148 South Freeway 6201, Texas. FIG. 2 (a) shows an exemplary control device 100 that can be used with this device.

  The control device 100 is used to operate the ultrasonic handpiece 112 and includes a control console 114 comprising a control module or CPU 116, a suction vacuum or peristaltic pump 118, a handpiece power supply 120, and (INFINITI A perfusion flow or pressure sensor 122, such as a trademark system, and a valve 124. Various ultrasonic handpieces 112 and cutting tips, such as the ultrasonic handpieces and cutting tips described in US Pat. It can be used without limitation. The CPU 116 may be any suitable microprocessor, microcontroller, computer, or digital logic controller. Pump 118 may be a peristaltic pump, a diaphragm pump, a venturi pump, or other suitable pump. The power supply source 120 may be any ultrasonic driver. The perfusion pressure sensor 122 may be a variety of commercially available sensors. The valve 124 may be any suitable valve, such as a solenoid operated pinch valve. Infusion of a perfusate such as saline may be a commercially available perfusion solution provided in a bottle or bag, but may also be performed by a saline source 126.

  In use, perfusion pressure sensor 122 is connected to handpiece 112 and perfusate source 126 via perfusion lines 130, 132, 134. The perfusion pressure sensor 122 measures the flow rate or pressure of the perfusate from the perfusate source 126 to the handpiece 112 and provides the information to the CPU 116 via the cable 136. The CPU 116 uses the perfusate flow rate data to control the operating parameters of the control console 114 using software commands. For example, the CPU 116 changes the output of the power supply source 120 sent to the handpiece 112 and the distal end portion 113 via the cable 142 via the cable 140. The CPU 116 also uses data supplied by the perfusion pressure sensor 122 to change the operation of the pump 118 and / or valve via the cable 144. Pump 118 aspirates perfusate from handpiece 112 via line 146 and into collection container 128 via line 148. The CPU 116 also sounds an audible sound to the user using data provided by the perfusion pressure sensor 122 and the matched output of the power supply 120. Further details regarding such a surgical device are disclosed in US Pat.

  The control console 114 is programmed to control and manipulate the pulses transmitted to the handpiece 112 and to control the output of the handpiece pulses used during surgery. Referring to FIGS. 2 (b) and 2 (c), a pulse occurs in a packet or in an on period and an off period. In the illustrated embodiment, the pulse is a 50% duty cycle. In fact, on-time, off-time, and duty cycle can be used in a variety of applications.

  The following description assumes that a maximum power level of 100% is the maximum power reached (ie, the maximum stroke or displacement of the ultrasound tip). In other words, 50% output represents half of the maximum reached output. The output level is expressed as a percentage (%) of the maximum achieved output. Embodiments of pulse manipulation used in the above-described exemplary phacoemulsification surgical device are shown in FIGS. 3-21 and include a microburst of pulses as shown in FIGS. 2 (b) and 2 (c) or It is organized like a packet. A packet or burst of pulses is provided to the ultrasound handpiece to generate a substantially corresponding output at the ultrasound tip.

  Referring to FIG. 3, according to one embodiment, one or both of the rising component 310 and the attenuation component 320 of each pulse 300 are programmed separately from the natural rise and natural decay. For example, the rising component 310 and the attenuation component 320 are programmed with a linear function and / or a non-linear function separately from the natural rise and natural decay caused by switching the amplifier on and off to generate a pulse. . For those skilled in the art, some pulses (eg, square and rectangular pulses) are commonly represented as “ideal” square or rectangular pulses with an immediate sharp transition between low and maximum power levels. Will be clear. In practice, however, such pulses have a natural rise time and a natural decay time, such as, for example, an exponential rise time or an exponential decay time caused by a load or impedance. For example, the standard natural decay time is about 4 milliseconds (ms). On the other hand, embodiments control the linear rise time and linear decay time separately from the natural transition caused by switching the amplifier on and off by setting or programming the rise function and / or decay function. It is intended for.

  Controlling the ascending component 310 and the attenuating component 320 and the ascending time 312 and the attenuating time 322 is advantageous because various pulse shapes can be generated for specific surgical applications and surgical devices. For example, a pulse having a rising component 310 that is programmed so that the output gradually increases allows the lens material to be more accurately aligned. For example, a gradual output transition does not prematurely push the lens material away from the tip of the handpiece. On the other hand, known devices that use pulses with sharp transitions from minimum to maximum inadvertently press the lens material quickly away from the tip, thus complicating surgery. Thus, pulses with programmed ascending components can improve the effectiveness of the alignment and cutting of the lens material and the surgical procedure. Furthermore, by programming the attenuation component and the pulse time, less energy can be transferred to the eyeball, resulting in less tissue heating.

  According to one embodiment, the programmed rise and / or decay components are programmed according to a linear function. In the embodiment shown in FIG. 3, each pulse 300 is programmed with two linear components: a linear rise component 310 and a linear decay component 320. The linear rise component 310 increases from the first amplitude to the second amplitude. The intermediate component 330 extends between the linear rise component 310 and the linear decay component 320 with a second amplitude. The linear attenuation component 320 decreases from the second amplitude to the third amplitude.

  The linear rise component 310 has a linear rise time 312, the linear decay component 320 has a linear decay time 322, and the maximum amplitude component 330 has a maximum amplitude time or active time or “on” time 332. In general, since more time is required to reach a higher power level, the linear rise time 312 and the linear decay time 322 vary depending on the maximum power level of the pulse.

  In one embodiment, the linear rise time 312 is programmed from about 5 ms to about 500 ms. If the pulse needs to reach 100% power, the duration of the linear rise time 312 will be longer. However, if the pulse only needs to reach an output less than 100%, the linear rise time 312 can be made shorter, for example, less than 5 ms or about 5 ms. The duration of the linear rise time 312 increases with increasing power level and can be suitably programmed using the control console 114. If necessary, the rate at which the linear component increases can be limited to protect output components such as amplifiers.

  According to one embodiment, the linear decay time 322 is programmed from about 5 ms to about 500 ms. In one embodiment, the linear decay time 322 is such that the output of the control console 114 is such that the output decays linearly, about 70% of the output dissipates within about 2 ms and about 98% of the output dissipates within about 4 ms. Has been programmed using. The linear decay time 322 may be longer, the same or shorter than the linear rise time 312. For example, FIG. 3 shows a linear decay time 322 that is longer than the linear rise time 312. The linear decay time 322 can be longer or slower than the natural decay time. Also, the rate of rise and decay may be the same so that the pulse is symmetric and has both programmed rise and decay components.

  The maximum amplitude time or active time or “on” time 332 can be varied in various applications. The maximum amplitude time is about 5 ms to about 500 ms. In the illustrated embodiment, the intermediate component 330 has a constant amplitude (with a second amplitude). In another embodiment, the duration of the maximum amplitude time is less than 5 ms taking into account the resulting heat, for example, depending on the required power. In yet another embodiment, the amplitude varies across the intermediate component 330 such that it increases or decreases, for example, between the linear rise component 310 and the linear decay component 320.

  In the illustrated embodiment, the linear rise component 310 begins at a non-zero level. In another embodiment, the linear rise component 310 begins at a zero level. The initial power level depends on the particular surgical procedure and the configuration of the surgical device. Similarly, the linear attenuation component 320 may end at a zero or non-zero output level. FIG. 3 shows approximately the same first and third amplitudes. In another embodiment, they may be different. For example, the third amplitude at the end of the linear attenuation component 320 may be greater than the first amplitude.

  In another embodiment, the programmed rise component and / or decay component may be a non-linear component. The non-linear component may be programmed according to a logarithmic function, an exponential function, and other non-linear functions. FIG. 3 shows a linear rise component and a linear decay component for purposes of illustration and not limitation. However, one or both of the rising component and the damping component may be programmed with a non-linear function.

  Referring to FIG. 4 according to another embodiment, rather than having an intermediate component 330 as shown in FIG. 3, the pulse 400 has a linear rise component 310 and a linear decay component 320 that intersect at a second amplitude maximum point 410. It has been programmed. In the illustrated embodiment, the programmed rise time 312 and decay time 322 are equal. The linear rise component 310 and the linear attenuation component 320 intersect at the midpoint. In another embodiment, the linear rise time 312 and the linear decay time 322 are programmed from 5 ms to 500 ms, as described above with respect to FIG. Thus, the rise time and decay time are not equal and the maximum point 410 is not an intermediate point.

  With reference to FIGS. 5-8 for another embodiment, pulses having one or more linear and / or non-linear components are combined with other pulses and pulse patterns. For purposes of illustration and not limitation, FIGS. 5-8 show pulses with programmed linear components, but one or more programmed linear components can be replaced with programmed nonlinear components.

  FIG. 5 shows a first rectangular pulse 510, a second rectangular pulse 520, a pulse 530 with a linear decay component, a pulse 540 with a linear rise component, and a linear rise component and linear, similar to the pulse shown in FIG. An array or combination 500 of pulses having a pulse 550 with an attenuation component is shown.

  FIG. 6 is similar to the pulse shown in FIG. 3 in that a pulse 610 with linear rise and decay components and an intermediate component, a rectangular pulse 620, a rectangular pulse 630 with a longer duration than pulse 620, and a linear decay. FIG. 9 shows an arrangement or combination 600 of pulses according to another embodiment having a pulse 640 with a component and a pulse 650 with a linearly rising component.

  FIG. 7 shows a pulse 710 with a linear decay component, a multi-segment rectangular pulse 720 with a decreasing amplitude, a pulse 730 with a linear decay component, a pulse 740 with a linear decay component, and the pulses shown in FIG. Similarly, yet another embodiment of a pulse arrangement or combination 700 having a pulse 750 with both a linear rise component and a linear decay component and another rectangular pulse 760 is shown.

  FIG. 8 shows yet another embodiment of an array or combination 800 of pulses having the same maximum amplitude and at least one pulse having a linear component. Specifically, FIG. 8 includes a pulse 810 with a linear attenuation component, a multi-segment rectangular pulse 820 with a decreasing amplitude, a pulse 830 with a linear attenuation component, a pulse 840 with a linear attenuation component, Similar to the pulse shown in FIG. 4, a pulse 850 having both a linear rise component and a linear decay component and a rectangular pulse 860 are shown.

  As shown in FIGS. 5-8, each pulse in a packet of pulses is compared to other pulses based on, for example, different amplitude, duration, shape, number of programmed linear components and / or power. Has distinguishable properties. In addition, the pulse combinations include different numbers of pulses, different numbers of rectangular and square pulses, different numbers of pulses with multiple linear components, different numbers of pulses with one linear component, and two linear There are different numbers of pulses with components and different numbers of pulses with two linear components and components of constant amplitude. Thus, in an embodiment, the surgeon customizes the pulse to suit a particular surgical and phacoemulsification device.

  As shown in FIGS. 5-8, a rectangular pulse and a pulse comprising one or more linear components can be at various positions and at, for example, the beginning or end of the pulse sequence, or somewhere in between. Can be arranged in an array. The order of rectangular pulses (or other shaped pulses) and pulses with a linear component can be varied depending on the surgical application and device used. Some pulses may be grouped or mixed with other types of pulses.

  For example, referring to FIG. 5, rectangular pulses 510 and 520 are grouped and pulses 530, 540, 550 with linear components are grouped. In another embodiment, the one or more non-rectangular pulses are between rectangular pulses such that the rectangular pulses are intermingled with various types of pulses. Similarly, one or more pulses without a linear component may be located between pulses with a programmed linear component.

  In another embodiment, referring to FIGS. 9-14, pulses with programmed linear components are included in a pattern of pulses with each pulse having a continuously decreasing or increasing output. FIGS. 9-11 show an array of pulses with an output where each pulse is continuously higher, and FIGS. 12-14 show an array of pulses with an output where each pulse is continuously decreasing.

  Referring to FIG. 9, another embodiment has an array or combination 900 of pulses comprising pulses 910, 920, 930, 940, 950, each of which is similar to the pulse shown in FIG. Each successive pulse has a higher output (P1 to P5) than the previous pulse. For example, the pulse 930 has an output P3 that is greater than the output P2 of the pulse 920.

  FIG. 10 shows another embodiment in which the pulse arrangement or combination 1000 comprises pulses 1010, 1020, 1030, 1040, 1050, each of which is similar to the pulse shown in FIG. Each successive pulse has a higher output than the previous pulse.

  FIG. 11 shows yet another embodiment in which the pulse arrangement or combination 1100 comprises a pulse comprising pulses of various shapes and sizes, such as a rectangular pulse, and at least one pulse comprising a linear component. Each successive pulse has a higher output than the previous pulse. An array or group of pulses with an initial low power level and a subsequent increasing power level effectively increases the lens material at the tip of the ultrasonic handpiece while gradually increasing the power to emulsify the lens material. It is effective to hold and control.

  Referring to FIG. 12 according to another embodiment, an array or combination 1200 of pulses comprises pulses 1210, 1220, 1230, 1240, 1250, each of which is similar to the pulse shown in FIG. Each pulse comprises a programmed linear rise component 310 and a programmed linear decay component 320. Each pulse has a reduced output compared to the previous pulse. For example, the pulse P3 is an output smaller than the pulse P2, and the pulse P4 is an output lower than the pulse P3.

  In another embodiment, referring to FIG. 13, the pulse arrangement or group comprises pulses 1310, 1320, 1330, 1340, 1350. Each pulse is similar to the pulse shown in FIG. 4, and each pulse has a reduced output compared to the previous pulse. FIG. 14 shows yet another embodiment of an array or combination 1400 of pulses 1410, 1420, 1430, 1440, 1450 with an output that decreases with time. The combination 1400 comprises pulses having various shapes and sizes, such as rectangular pulses, and pulses with linear components.

  Referring to FIGS. 15-19, another embodiment is directed to converting pulses between different pulse modes depending on a controller such as a foot pedal or foot switch. According to one embodiment, the pulses are converted between burst mode and pulse mode. The pulse pattern is shown in relation to four foot pedal positions that may or may not be defined by a detent or position indicator. It will be apparent to those skilled in the art that the foot pedal or foot switch may have other numbers of positions and that the transitions described herein may be made by pressing and releasing the foot pedal.

  Referring to FIG. 15, the “burst” mode provides a series of pulses 1500 of constant amplitude and constant amplitude of ultrasound output, each followed by an “off” time 1510. The off time 1510 between pulses 1500 is controlled by input by the surgeon by moving or pressing the foot pedal. In other words, in burst mode, each pulse 1500 has a fixed “on” time 1520 and a variable “off” time 1510, which is adjusted based on the user's foot pedal operation. Burst mode pulses have an active time of about 5 ms to about 500 ms. The burst or “off time” interval is from about 0 ms to about 2.5 s (when the foot pedal is low enough and the output lasts). The off time depends on the application and equipment, for example, the desired amount of cooling or heat dissipation required. The pulse in the burst mode is a pulse in the “fixed burst” mode as shown in FIG. 15 or a pulse in the “linear burst” mode as shown in FIG. For the fixed burst mode, depressing the foot pedal reduces the off time 1510 while the pulse amplitude remains constant. For the linear burst mode, depressing the foot pedal reduces the off time 1500 and further adjusts the amplitude. In the illustrated embodiment, the amplitude is increased by depressing the foot pedal. Thus, for both the fixed burst mode and the linear burst mode, the output “off” time 1510 may be adjusted and the amplitude of the pulse may or may not be adjusted.

  In particular, FIGS. 15 and 16 show the foot pedal in four positions. When the foot pedal is initially at position 1 and pressed to position 2, the off time 1510 decreases. The number of fixed-width, constant-amplitude pulses 1500 increases as the foot pedal is depressed. When the foot pedal is depressed from position 2 to position 3, the off time 1510 eventually reaches a predetermined off time 1510, eg, an on time 1520 or another suitable time. By further depressing the foot pedal from position 3 to position 4, the off time 1510 is reduced to zero, ie 100% on time 1520 (persistent mode). A similar process is illustrated in FIG. 16 except that the pulse is a linear burst mode pulse and that the amplitude of the pulse increases when the foot pedal is moved between different positions.

  Referring to FIG. 17 for the “pulse” mode, the amplitude of the fixed width pulse 1700 varies according to the position of the foot pedal. In the illustrated embodiment, the amplitude is increased by depressing the foot pedal.

  Referring to FIGS. 18 and 19, another embodiment is directed to converting pulses between burst and pulse modes in response to foot pedal movement. FIG. 18 shows the transition from the burst mode to the pulse mode. The foot pedal is pressed from position 1 to position 2 to reduce the off time 1510. The off time 1510 further decreases when the foot pedal is pressed from position 2 to position 3. As the foot pedal is further depressed, the number of fixed-width, constant-amplitude pulses increases over a period of time. When the foot pedal is further depressed, the off time 1510 eventually reaches a predetermined value, such as the on time 1520 or another suitable value. In the illustrated embodiment, the predetermined value is equal to the on time 1520. The amplitude of the pulse is then adjusted after the off-time 1510 is equal to the on-time 1520 (or another suitable value), thereby increasing the energy generated by the handpiece and causing the pulse from burst mode to pulse mode. Convert it.

  In another embodiment, referring to FIG. 19, the pulses are converted from pulse mode to burst mode pulses. When the device is initially in pulse mode and the foot pedal is depressed to position 4, the amplitude of the pulse is reduced by first releasing the foot pedal. After the amplitude has reached a predetermined amplitude, further releasing the foot pedal will adjust the burst mode and increase the output “off” time 1510, thereby cooling the ultrasound tip 113. In addition, the pulse 1500 having a smaller fixed width and a smaller output are provided to the ultrasonic tip 113 in a certain time.

  As shown in FIGS. 18 and 19, the surgeon can advantageously switch between burst mode and pulse mode by operating a single controller, for example, pressing and releasing the foot pedal. It is. This process is particularly advantageous because these conversions are accomplished without interruption and adjustment in other ways related to changing to different pulse modes, such as adjusting parameters on a display screen or interface. It is. Instead, the embodiment also allows for continuous pulse transitions by pressing and releasing the foot pedal as part of the natural continuous movement of the surgeon's leg, thereby allowing the surgical instrument to This is advantageous because it simplifies shape and operation and simplifies surgery.

  In yet another embodiment, referring to FIG. 20, the output amount of each pulse can be gradually increased by utilizing a multi-step pulse or a multi-segment pulse 2000. It will be apparent to those skilled in the art that multi-segment pulses may have two, three, four, and other numbers of segments. Accordingly, the two segment pulses shown in FIG. 20 are provided for purposes of illustration and not limitation.

  In the illustrated embodiment, the first step 2010 is a smaller output than the subsequent step 2020. For example, as shown in FIG. 20, the first pulse segment 2010 has a first amplitude for a predetermined time, and then the second pulse segment 2020 has a second amplitude for a predetermined time. Low power, as opposed to abrupt transitions, typically rectangular, from low to maximum power levels that cause the lens material to inadvertently leave the tip during cutting of the lens material By constructing multi-segment pulses that gradually transition from to higher power, the ability to hold and emulsify the lens material more accurately is provided. Referring to FIG. 21 in another embodiment, multi-segment pulse 2100 may have more than two increasing amplitude segments. In the illustrated embodiment, the pulse has three pulse segments 2110, 2120, 2130. Other pulses may have four, five, and other numbers of pulse segments as desired.

  The various pulses and pulse patterns described above are pulses of ultrasonic energy that are transmitted in packets to the transducer elements of the handpiece. For example, as shown in FIGS. 2 (b) and 2 (c), ultrasonic energy is transmitted to the piezoelectric element as intermittent packets of pulses separated by an off period. The pulse patterns according to another embodiment of the invention described above are transmitted to the piezoelectric elements of the ultrasonic handpiece during these “on” times and within these packets.

  For example, FIG. 22 shows a packet of pulses of ultrasonic energy having a continuously increasing output as shown in FIG. As another example, FIG. 23 shows a packet of pulses of ultrasonic energy having a continuously decreasing output, as shown in FIG. For those skilled in the art, it is clear that a packet may have one or more groups of pulses, and that a packet may end at the end of one group of pulses or in the middle of one group of pulses. I will. For example, FIGS. 22 and 23 show a packet ending with a second pulse in one group of pulses. The packet may also end with the last pulse in the group of pulses. Accordingly, FIGS. 22 and 23 are provided for purposes of illustration and not limitation. It will also be apparent to those skilled in the art that the pulse embodiments described herein do not need to be configured or grouped into packets to control the ultrasound handpiece.

  Although reference has been made to the above description for various embodiments, it will be understood by those skilled in the art that improvements, changes, and substitutions that do not occur to the described embodiments can be made without departing from the scope of the embodiments. Will be clear.

DESCRIPTION OF SYMBOLS 100 Control apparatus 112 Handpiece 114 Control console 116 CPU
118 Pump 120 Power supply 122 Pressure sensor 124 Valve 300 Pulse 310 Rising component 312 Rising time 320 Attenuating component 322 Decreasing time 330 Intermediate component 332 On-time 510 First rectangular pulse 520 Second rectangular pulse 530 Pulse with linear damping component 540 Linear Pulse with rising component 550 Pulse with linear rising component and linear damping component

Claims (9)

In a method of generating energy for use in an ophthalmic surgical instrument, comprising: generating a burst mode pulse; and converting the burst mode pulse into a pulse mode pulse in accordance with a controller ;
The step of generating the burst mode pulse comprises the step of generating a pulse having an on time, a first off time, and a first amplitude, and the step of converting the burst mode pulse depends on the controller Reducing the first off-time of the pulse to a second off-time, and when the second off-time reaches a predetermined value, the amplitude of the pulse from the first amplitude to the second amplitude according to the controller And increasing the process,
The predetermined value includes the ON time, and the step of increasing the amplitude of the pulse from the first amplitude to the second amplitude starts after the second OFF time becomes substantially the same as the ON time. A method characterized by that.   The method according to claim 1, wherein the controller is a foot pedal, and the step of converting is performed in response to movement of the foot pedal.   The method of claim 2, wherein the converting step begins after the foot pedal reaches a predetermined position.   The method of claim 1, wherein generating the burst mode pulse comprises generating a rectangular pulse.   The method of claim 1, wherein the on-time is stationary during the converting step. In a method of generating energy for use in an ophthalmic surgical instrument, the method includes: generating a pulse in a pulse mode; and converting the pulse in the pulse mode into a burst mode in response to a controller ;
The step of generating the pulse mode pulse includes the step of generating a pulse having an on time, a first off time, and a first amplitude, and the step of converting the pulse mode pulse depends on the controller Reducing the amplitude of the pulse from the first amplitude to the second amplitude, and increasing the first off time to a second off time according to the controller when the second amplitude reaches a predetermined amplitude. And
The method wherein the on-time is stationary during the converting step . The method according to claim 6 , wherein the controller is a foot pedal, and the step of converting is performed in response to movement of the foot pedal. The method of claim 7 , wherein the converting step begins after the foot pedal reaches a predetermined position. The method of claim 6 , wherein the step of generating a pulse mode pulse comprises the step of generating a rectangular pulse.

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