Particle contact detection method, console of an ophthalmic surgical system, and ophthalmic surgical system

Abstract

The invention relates to a method for detecting contact of a particle (19) with a treatment needle (6) of an ophthalmological surgical handpiece (2), wherein the treatment needle (6) can be driven by an oscillation of an electrical drive unit (10), for which a time-varying electrical drive signal is applied to the electrical drive unit (10) at least intermittently by a generator unit (15). According to the invention, in a low-oscillation state of the treatment needle (6), the treatment needle (6) is oscillated with a maximum first oscillation amplitude (A1), an electrical contact signal (35) of the electrical drive unit (10) is detected on the basis of a second oscillation amplitude (A2) of the treatment needle (6), wherein the second oscillation amplitude (A2) is greater than the first oscillation amplitude (A1), the detected electrical contact signal is evaluated, and contact of the particle (19) with the treatment needle (6) is determined on the basis of the evaluation.

Description

[0001] The invention relates to a console of an ophthalmic surgical system for operating an ophthalmic surgical handpiece, which ophthalmic surgical handpiece is connectable to the console and comprises a treatment needle and an electrical drive unit for driving the treatment needle by oscillation. The console comprises at least one generator unit for providing a time-varying electrical drive signal for the electrical drive unit. Finally, the invention also relates to an ophthalmic surgical system for treating an eye, which has at least one ophthalmic surgical handpiece for operating on the eye lens. The ophthalmic surgical handpiece comprises a treatment needle and an electrical drive unit for driving the treatment needle by oscillation. The ophthalmic surgical system further comprises a console for operating the ophthalmic surgical handpiece, which ophthalmic surgical handpiece is connectable to the console at least during the intended operation. The console comprises a generator unit, which is couplable to the handpiece and is for providing a time-varying electrical drive signal for the electrical drive unit of the handpiece.

[0002] The ophthalmic surgical system, the console and the handpiece are especially used for treating a lens opacity of a biological, e.g. human or animal, eye lens. In medicine, a lens opacity is also known as a cataract or the like. One possibility of treating a lens opacity is to replace the eye lens by an artificial lens. For example, phacoemulsification is a technique for treating a lens opacity. Phacoemulsification can be performed by means of an ophthalmic surgical system.

[0003] One important component for performing phacoemulsification is an ophthalmic surgical handpiece, in the following referred to as handpiece only. The handpiece comprises a treatment needle, which is mechanically connected to a handpiece drive unit. During the intended operation, the treatment needle is driven by oscillation of the drive unit. Typically, the tip of the driven needle is driven to perform vibrations in the ultrasonic range, e.g. in the range of about 10 kHz to about 80 kHz. When the tip of the treatment needle is in contact with the eye lens to be exchanged or replaced, this leads to emulsification, i.e. pulverization, of the eye lens and releases lens fragments or particles. Typically, during the treatment of phacoemulsification, a flushing fluid is supplied to the eye. At the same time, an aspiration fluid is withdrawn from the surgical area of the eye. For this purpose, the treatment needle is typically designed as a hollow needle, whereby a part of the aspiration line with an opening in the tip region can be provided. The particles released during emulsification of the eye lens are removed from the surgical area via the aspiration line together with the aspiration fluid. After the eye lens has been removed in this way, an artificial eye lens is implanted in its place. This basically completes the treatment of the eye and the vision can be at least partially restored.

[0004] It is known that due to the mechanical ultrasonic movement of the treatment needle, heat can be generated during the treatment of the eye for reasons of friction and the like. Firstly, this reduces the effectiveness in connection with the emulsification of the eye lens, and secondly, it leads to an unwanted input of a large amount of heat locally in the eye, which can cause irreversible damage to the eye. Further, especially in the case of a longitudinal oscillation of the needle tip of the treatment needle, lens fragments or particles to be flushed or already adhering lens fragments or particles can be pushed away. This can prolong the time required for the operation, which can also increase the energy input into the eye, thus leading to the generation of heat. Against this background, DE 10 2010 047 009 A1 discloses a control device for an ophthalmic surgical system, which allows the power of the drive unit to be controlled on the basis of particle properties of the particles determined by means of an optical system.

[0005] According to the teaching of DE 10 2010 047 009 A1, a separate optical system is required, and also image processing, in order that the particle properties can be determined, on the basis of which the amount of ultrasonic energy supplied to the handpiece can be controlled. If the image processing is carried out with high resolution, relatively comprehensive signal processing can be required, and a significant delay in the adjustment speed can result.

[0006] US 20050261715 A1 describes a control system for operating an ultrasonic handpiece for emulsifying an eye lens, the ultrasonic handpiece comprising a control console. The ultrasonic handpiece is connected to a power supply in the control console by means of a power cable. The control console comprises a CPU which is able to change the output power of the power supply transmitted to the ultrasonic handpiece and to the cutting tip of the ultrasonic handpiece by means of the cable. A piezoelectric crystal in the ultrasonic handpiece is driven by this output power and oscillates, thereby outputting ultrasonic energy. A connector is connected to the output of the power supply or to the power cable. The connector itself is coupled to current and voltage feedback components of the control system. The feedback components are used to carry out voltage and current measurements during detection intervals, in which less power (detection power) is supplied to the handpiece, and these detection intervals alternate with cutting intervals, in which more power (cutting power) is supplied. The measurements are based on the mechanical stress to which the piezoelectric crystal in the handpiece is subjected when the tip contacts tissue. During the detection intervals, a power value is calculated from the measured voltage and the measured current, and the contact of the tip with a material such as an eye lens is determined from an increase in the power value. The control system is thus able to detect when the cutting tip is no longer in contact with the eye lens tissue or when it is in contact with a different part of the eye lens tissue of different hardness, and to adjust the power supplied to the ultrasonic handpiece during the cutting intervals. The power supplied to the ultrasonic handpiece during the detection intervals is always greater than zero, so that tissue can still be cut here, and this power should be greater than zero in order that a load on the tip can be detected.

[0007] US2021361481A1 discloses a phacoemulsification device comprising a console. A phacoemulsification probe is connected to the console via a cable. The phacoemulsification probe contains a piezoelectric actuator within, in order to allow a needle configured to be inserted into the ocular lens capsule of an eye to oscillate in one or more resonant modes. To this end, the console comprises a piezoelectric drive system, which is coupled to the piezoelectric crystals of the actuator by the cable. Through the cable, a drive module of the drive system provides a processor-controlled drive signal to the piezoelectric actuator to adapt the frequency of the multi-resonant mode of the piezoelectric actuator, so that the needle maintains a maximum oscillation amplitude. The direction and amplitude of the needle displacement are estimated using a magnetic sensor in the phacoemulsification probe, which are used by the processor and the drive module to control the actuator via the cable to maintain the needle resonant oscillation. The processor calculates the derivative of the magnetic sensor output signal over time, and when this derivative exceeds a threshold, the user is notified of contact with the ocular media, i.e. the ocular lens.

[0008] The problem addressed by the present invention is to develop a console and an ophthalmic surgery system, the effect of which is inter alia to be able to further reduce the heat input during the treatment of the eye, thus enabling a relatively fast and reliable treatment of the eye.

[0009] As a solution, the present invention proposes a console and an ophthalmic surgery system as recited in the independent claims.

[0010] Advantageous developments emerge from the features of the dependent claims.

[0011] The present invention proposes that in the low oscillation state of the treatment needle, which oscillates with a maximum first oscillation amplitude, an electrical contact signal of the electrical drive unit is detected on the basis of a second oscillation amplitude of the treatment needle, which is greater than the first oscillation amplitude, that the detected electrical signal is evaluated and that the contact of the particle with the treatment needle is determined on the basis of the evaluation.

[0012] With regard to the general console, the present invention proposes in particular that the console comprises a detection unit electrically couplable to the drive unit, which detection unit is adapted to detect an electrical contact signal of the electrical drive unit on the basis of a second oscillation amplitude in the low oscillation state of the treatment needle, which oscillates with a maximum first oscillation amplitude, said second oscillation amplitude being greater than the first oscillation amplitude. The console further comprises an evaluation unit for evaluating the detected electrical contact signal and determining the contact of the particle with the treatment needle on the basis of the evaluation.

[0013] With regard to the general ophthalmic surgery system, the present invention proposes in particular a console designed according to the present invention.

[0014] The application is based, inter alia, on the idea that the therapeutic needle is usually only to be driven by means of oscillation when it is in contact with the eye lens or with a fragment or particle of the eye lens to be replaced. By means of the application, it is recognized that the drive unit is not limited to unidirectional use for driving the therapeutic needle by means of oscillation; rather, it can also be used in reverse, in particular when the therapeutic needle is in contact with a lens fragment or particle, an electrical contact signal being output on the basis of the movement of the therapeutic needle. As a result, contact of a lens fragment or particle with the therapeutic needle can be determined by means of a suitable evaluation of the electrical contact signal provided by the drive unit accordingly. In this case, the application also makes use of the knowledge that the drive unit can usually be operated bidirectionally. That is, the application of an electrical drive signal can result in a mechanical movement of the therapeutic needle, and vice versa, a mechanical movement of the therapeutic needle can result in an electrical contact signal. The application thus makes use not only of the drive function of the drive unit, but also enables the sensor function of the drive unit at the same time.

[0015] The application makes use, inter alia, of the effect that contact of the therapeutic needle with a particle results in a mechanical movement of the therapeutic needle and this, as a result of the mechanical coupling to the drive unit, results in an electrical contact signal of the drive unit. Depending on the design of the drive unit, the electrical contact signal can be, for example, an electrical current or a voltage. The detection unit is designed to be suitably adapted to the electrical contact signal, enabling reliable detection of the electrical contact signal output by the drive unit. It goes without saying that the corresponding statements also apply to the drive signal provided by the generator unit. The drive signal is a time-varying electrical drive signal, which can be, for example, a time-varying voltage, in particular an AC voltage, or a time-varying current, in particular an alternating current. The generator unit is suitably designed in order to be able to provide the drive signal.

[0016] The electrical drive signal is usually an AC voltage provided by the generator unit. To this end, the generator unit can comprise an electrical energy transducer or electrical energy converter in the form of an inverter, a converter or the like. The electrical drive unit can be designed as an electrostatic drive unit or as an electromagnetic drive unit. As an electrostatic drive unit, the drive unit can be designed in a piezoelectric-based manner. To this end, the drive unit can comprise one piezoelectric element or a plurality of piezoelectric elements which are mechanically and electrically connected to one another in a suitable manner. The piezoelectric-based drive unit thus formed allows the use of the effect that, on application of an AC voltage as an electrical drive signal to the piezoelectric elements, their mechanical dimensions, for example their position, etc., change. The therapeutic needle is mechanically connected to the piezoelectric-based drive unit and can thus achieve the desired drive effect during the intended operation. In the case of an electromagnetic drive unit, an electro-mechanical transducer can be provided accordingly, for example, which can be acted upon by an alternating current as an electrical drive signal. For example, using an alternating magnetic field, a magnetizable actuator of the transducer can be actuated in order to be able to generate the desired mechanical movement. Usually, the electrical drive unit has electrical terminals to which the electrical drive signal can be applied, thereby achieving the desired mechanical movement of the therapeutic needle.

[0017] The generator unit is preferably an electronic unit designed to provide an electrical control variable for the electric drive unit. To this end, the generator unit can comprise an electronic circuit, for example an inverter or the like. Furthermore, the generator unit can of course also comprise a control unit in the form of a hardware circuit, in particular a programmed computer unit, which can be provided as a supplement or alternative to the hardware circuit. The generator unit thus provides an electrical drive signal. The generator unit is designed to provide the electrical drive signal in a time-varying manner, preferably in an oscillating manner. The oscillation frequency is preferably greater than about 10 kHz, particularly preferably about 40 kHz. Depending on the type of electrical power provided to the drive unit, the amplitude of the oscillation or the like can be set by the generator unit. Of course, the electrical drive signal can also be provided in a clocked manner, for example in the form of a pulse sequence, for example a burst or the like. In order to be able to obtain a specific, predefinable type of oscillation of the treatment needle, the generator unit can also provide the electrical drive signal at a plurality of frequencies and corresponding respective amplitudes and phase angles relative to one another.

[0018] The application makes use of the idea, inter alia, that in the non-oscillating or low-oscillating state of the treatment needle, the drive unit is able to provide an electrical contact signal as soon as it comes into contact with a particle. Since the detection unit is able to be coupled to the electrical drive unit, the electrical contact signal from the drive unit can be detected by the detection unit. The movement of the treatment needle with regard to the oscillation caused by the drive signal should therefore decay to such an extent that the contact signal can be reliably detected by the detection unit. To this end, it can be provided, for example, that after the generator unit deactivates the drive signal, the decay of the detection of the treatment signal oscillation is detected, and as soon as the detected signal is less than a specified or specifiable comparison value, the detection of the electrical contact signal from the drive unit is activated in the detection unit. Thereby, decoupling of the drive function of the drive unit from the sensor function can be achieved. The application thus uses the handpiece as a sensor unit, inter alia, on the basis of the intended use during phacoemulsification treatment. The application is based, inter alia, on the idea that the handpiece is used as a sensor unit in addition to the intended use during phacoemulsification treatment.

[0019] Preferably, the oscillation state of the treatment needle caused by the drive unit comprises not only the oscillation of the treatment needle when the electrical drive signal from the generator unit is applied to the drive unit, but also a decay phase after the generator unit deactivates the electrical drive signal, during which the oscillation of the treatment needle at least partially decays. Typically, the treatment needle will continue to oscillate for a limited decay phase after the electrical drive signal is deactivated until the oscillation of the treatment needle substantially decays, preferably completely, due to the damping of the oscillation. Overall, the present application enables the detection of the contact of the particle with the treatment needle without the need for additional measures to be implemented on the ophthalmic surgical handpiece. This means that this additional functionality can be achieved with relatively little outlay in terms of retrofitting the ophthalmic surgical system, in particular the control console. The low oscillation state represents a state in which the treatment needle does not oscillate or at most has a first oscillation amplitude. The contact of the particle with the treatment needle leads to a second oscillation amplitude of the treatment needle, which is detected by the evaluation unit as an electrical contact signal from the electrical drive unit, wherein the second oscillation amplitude is greater than the first oscillation amplitude. In the low oscillation state, the drive unit is deactivated. Thus, the treatment needle is not driven by oscillation.

[0020] The evaluation of the detected electrical contact signal can comprise an evaluation of the curve profile, an evaluation of the period duration, an evaluation of the amplitude, etc. The evaluation can be carried out by an electronic evaluation unit suitable for this purpose, which can comprise hardware circuits and / or programmable computer units for this purpose. The evaluation unit can at least partially consist of the detection unit or the control unit of the control console. Through the evaluation, it can further be possible to determine the size, hardness or speed of the particle. For this purpose, within the scope of the evaluation, the electrical contact signal can be subjected to a suitable analysis. In this case, the evaluation can take into account parameters determined empirically at an early stage during production or initialization of the ophthalmic surgical system. The evaluation of the detected signal can also comprise a spectral analysis and statistical methods, for example, in order to be able to determine the direction of contact of the particle with the needle.

[0021] However, the present application not only applies to the detection of the contact of the particle with the treatment needle; it also particularly applies to the removal of blockages in the region of the treatment needle, in particular suction-related blockages. Since the ophthalmic surgical handpiece or its treatment needle only needs to be activated when in contact with the lens or particles of the lens, the present application enables a significant reduction in the heat input into the eye. Only when in contact with a particle or the lens does the treatment needle need to be operated in an oscillating manner by the drive unit. Thus, since the activation of the oscillation of the treatment needle can be reduced in this way, the treatment of the eye, in particular the lens, can be significantly improved, especially in terms of heat input. Furthermore, since the adverse hydrodynamic effects known from the prior art can be reduced, the removal of the particles from the suction fluid can also be improved at the same time.

[0022] It is particularly advantageous that the application can be combined with a function that allows at least partial automatic deactivation of the output of the drive signal, for example because no or hardly any particles are present, no longer in contact with the eye lens, etc. To this end, it can be provided, for example, to detect the presence of particles in the aspirated fluid, as disclosed in DE 10 2020 118 887 A1 or other documents. It is thus possible to achieve an operation of the handpiece in which the drive signal is essentially only output to the drive unit when the ultrasonic energy is needed for emulsification purposes. If there is no contact with any particles or the eye lens, the energy output can be terminated automatically and a detection mode can be activated. Of course, as an alternative or in addition, it can also be provided that the energy output is terminated manually by the surgeon. Overall, this makes it possible to significantly reduce the heat input into the eye.

[0023] One development provides that the electrical contact signal is detected in addition to the electrical drive signal applied to the electrical drive unit. This development allows the electrical line coupling the drive unit to the generator unit or control console to also be used for the detection of the electrical contact signal by the detection unit. Since generally the amplitude or deflection of the drive signal can be much larger than the electrical signal when a particle comes into contact with the treatment needle, it is not necessary to operate the detection unit when the drive signal is applied to the electrical drive unit. To this end, the detection unit can be separated from the electrical line by a separate switching device or switching unit in order to prevent overuse of the detection unit. This can be achieved, for example, by a mechatronic and / or electronic switching unit. Thus, the detection unit can be connected to the electrical line preferably as soon as the generator unit deactivates the drive signal. At the same time, this configuration allows the detection of the decay of the oscillation state of the treatment needle by the detection unit.

[0024] It is also proposed that the detection of the electrical contact signal is activated only after a specified time interval has elapsed from the moment at which the electrical drive signal ends. The specified time interval can be chosen, for example, such that the decay of the oscillation of the treatment needle reliably occurs after deactivation of the drive signal even in unfavorable cases. The start time of the specified time interval can be coupled to, in particular also coincide with, the deactivation time of the drive signal. To this end, an appropriate control signal can be provided by the control unit of the generator unit or control console, which control signal can trigger the start of the specified time interval. In addition, the expiration of the time interval can trigger an activation signal for the detection unit, which activation signal activates the detection unit to detect the electrical contact signal. This can result in an automatic timing, which ensures reliable operation of the detection unit.

[0025] Preferably, the time interval is determined on the basis of the mechanical damping of the oscillation of the treatment needle. For example, the time interval can have been determined on the basis of empirical measurements or the like. However, it can also be provided that the time interval is determined on the basis of the amplitude of the drive signal in the deactivated state in addition. Preferably, the time interval is determined such that the oscillation of the treatment needle has substantially decayed at the end of the time interval. Depending on the requirements, other values can be taken into account in addition or alternatively to the mechanical damping and / or the amplitude of the drive signal in order to determine the time interval if necessary. The time interval can be determined to be in the range of a few microseconds to a few milliseconds. However, the time interval is preferably shorter than 0.5 seconds.

[0026] It is also proposed that the detection of the electrical contact signal by the detection unit is deactivated when the generator unit is activated to output the electrical drive signal. This development takes into account the fact that in the active state of the drive unit, the amplitude of the drive signal is greater than the amplitude of the electrical contact signal, the detection unit can only carry out an unsatisfactory detection or capture or can not carry out a detection or capture at all. The operation of the detection unit is therefore unnecessary and can be deactivated, for example in order to save energy, to protect the detection unit from overuse, to avoid malfunctions or the like. For example, the deactivation can comprise an electrical separation of the detection unit from the drive unit. The electrical separation can be implemented by means of the switching unit explained above. However, it can also be provided that the detection unit can comprise a limiting unit which automatically deactivates the detection unit or only the evaluation when the signal value is greater than a further specified comparison value.

[0027] An advantageous development proposes that the generator unit is activated to output the electrical drive signal upon determination of the contact of the particle with the treatment needle. This development allows the treatment needle to automatically enter the active operating state or allows the generator unit to automatically be activated to output the electrical drive signal, so that the electrical drive signal is only provided when there is also contact with the particle or the eye lens. This can enable an improved control of the treatment needle and thus a particularly low heat input into the eye.

[0028] With regard to the console, it is further proposed that the generator unit and the detection unit are electrically connected in parallel on the side of the drive unit. The advantage of this configuration is that no additional electrical lines are required to connect the handpiece to the console or to establish an electrical connection between the console and the drive unit of the handpiece. The electrical line used to electrically connect the generator unit to the electrical drive unit can also be used by the detection unit to capture the electrical contact signal at the same time. Thus, no changes to the handpiece are required in order to implement the present application. Thus, the present application can also be applied to existing handpieces without the need for modifications. Therefore, the parallel connection of the generator unit and the detection unit is preferably provided on the side of the console. Furthermore, it is also possible for the generator unit and the detection unit to be designed at least partially as an integral unit, so that in this respect only a single component is required in the console. This has also been found to be advantageous, in particular when retrofitting an existing console for use with the present application. In this case, only the existing component with the generator unit needs to be replaced by a corresponding component comprising the generator unit in connection with the detection unit. Thus, the outlay on the console side can also be kept very low and the present application can thus be implemented in an ophthalmic surgical system overall with little outlay. In principle, it is also possible to electrically connect the generator unit and the detection unit in series on the side of the drive unit. In this case, the generator unit is preferably designed to allow an electrical connection of the detection unit and the drive unit which provides as little electrical resistance as possible when the generator unit stops providing the drive signal, in particular preferably an electrical short circuit.

[0029] Further features of the present application become apparent from the claims, the drawings and the description of the figures. The features and combinations of features mentioned in the above description and in the description of the figures and combinations of features mentioned in the above description and / or shown in the figures alone can be used not only in the specified combinations, but also in other combinations, without departing from the scope of the present application. Thus, embodiments of the present application which are not explicitly shown and explained in the figures, but which arise through the individual combination of features of the explained embodiments and which can be created by them, are also to be considered as included and disclosed. The disclosure is also to be considered as extending to combinations of embodiments and features, so that these combinations of embodiments and features do not have all the features of an independent claim as originally worded. Furthermore, the disclosure is to be considered as extending to combinations of embodiments and features which go beyond or depart from the combinations of features stated in the dependent claims, in particular through the explanations stated above.

[0030] Further advantages and features of the present application are explained with reference to the following figures, in which:

[0031] Figure 1 a schematic representation of an ophthalmic surgical handpiece of an ophthalmic surgical system for emulsifying the eye lens of a human eye during an intended operation is shown,

[0032] Figure 2 It shows having Figure 1 A schematic diagram of an ophthalmic surgical system with a handheld device and a control console, wherein the handheld device is detachably connected to the control console via a connecting cable.

[0033] Figure 3 It shows Figure 2 A schematic block diagram of the detection and evaluation units of the control console, which is electrically connected via connecting lines. Figure 1 The drive unit of the handheld device in the middle,

[0034] Figure 4 A schematic diagram is shown, illustrating a graph of the electrical contact signal from the drive unit of the handheld device, where the particle is in contact with the treatment needle of the handheld device.

[0035] Figure 5 It shows Figure 1 The diagram shows the tip of the treatment needle of the handheld device and the particles away from it.

[0036] Figure 6 As shown Figure 5 The diagram shows particles partially blocking the aspiration opening of the treatment needle.

[0037] Figure 7 As shown Figure 5 The diagram shows particles completely blocking the aspiration opening of the treatment needle.

[0038] Figure 8 As shown Figure 5 The diagram shows the particles making lateral contact with the tip of the treatment needle.

[0039] Figure 9 A schematic signal / time diagram is shown to compare the effects of the present invention with those of the prior art.

[0040] Figure 10 It shows Figure 4 A detailed schematic diagram, in which the curve is used to depict when the particles follow... Figures 6 to 8 The voltage at the electric drive unit of the handpiece when any of the treatment needles comes into contact.

[0041] Figure 1 An ophthalmic surgical system was shown. Figure 2 A schematic diagram of an ophthalmic surgical handpiece 2. The handpiece 2 includes a treatment needle 6, one end of which extends from a sleeve 5 connected to the housing of the handpiece 2. The treatment needle 6 is designed as a hollow needle and provides a portion of an aspiration line 3. On the treatment side, the treatment needle 6 includes a needle tip 7, which also provides an outlet opening for the aspiration line 3. The needle tip 7 is used to emulsify the lens 13 of the eye 9.

[0042] The handpiece 2 further comprises an electric drive unit 10, which in the present case is designed as a piezoelectric-based drive unit. The piezoelectric-based drive unit 10 comprises at least one piezoelectric element and preferably a stack of a plurality of piezoelectric elements (not shown here), which are mechanically connected to one another and to an end of the treatment needle 6 opposite the needle tip 7. The piezoelectric elements are also electrically connected to one another. It is thus possible to transmit the vibrations of the electric drive unit 10 to the treatment needle 6 in a manner dependent on a drive signal 36 Figure 4 ) in such a way that a suitable oscillatory movement of the needle tip 7 can be performed during the intended use.

[0043] For performing a treatment in the context of ophthalmic surgery, for example in the treatment of a cataract, the treatment needle 6, in particular the needle tip 7 thereof, is introduced into the region of the eye 9 to be treated, in particular into the region of the eye lens 13 to be treated. The excitation of the treatment needle 6 by the electric drive unit 10 produces ultrasonic oscillations, so that the eye lens 13 can be pulverized or emulsified. During the treatment, irrigation fluid is supplied via the irrigation line 4. At the same time, suction fluid is removed from the eye 9 via the suction line 3. At the same time, lens fragments or particles are removed from the eye 9 together with the suction fluid. During the treatment, the supply of irrigation fluid and the removal of suction fluid are preferably controlled in order to prevent the collapse of the anterior chamber of the eye 9.

[0044] Figure 2 A schematic diagram of an ophthalmic surgery system 100 is shown, which comprises a control console 1 connected via a connection line 14 to Figure 1 the handpiece 2 in . In the present configuration, it is provided that the connection line comprises, in addition to the electric line 11, also a portion of the suction line 3 and a portion of the irrigation line 4. The respective line portions of the irrigation line 4 and the suction line 3 are flow-coupled to corresponding line portions in the handpiece 2. In an alternative configuration, it can be provided that the connection line 14 has a multipart design, for example by providing respective separate tubes for the respective portions of the suction line 3 and the irrigation line 4. On the handpiece side, the connection line 14 can be firmly connected to the handpiece 2. On the other end of the connection line 14, a suitably designed attachment for detachably connecting the connection line 14 to the control console 1 is preferably provided. This is not depicted in the figure, however.

[0045] From Figure 2It is also apparent that the console 1 comprises a flushing fluid regulator 20 which is connected to the flushing line 4. The flushing fluid regulator 20 is also flow- connected to a flushing fluid reservoir 21. The flushing fluid regulator 20 is also communicatively connected to the control unit 8 of the console 1. The flow rate and / or the pressure of the flushing fluid in the flushing line 4 can be set by the flushing fluid regulator 20 in a manner dependent on a control signal from the control unit 8. For example, the flushing fluid reservoir 21 can be arranged to be integrated into the console 1. However, it can also be provided that the flushing fluid reservoir 21 is designed at least partially separate from the console 1 and connected to the flushing fluid regulator 20 via a separate line. In this case, a detachable connection can also be provided.

[0046] A corresponding structure can also be provided for the suction fluid. From Figure 2 It is apparent that the console 1 comprises a suction fluid regulator 22 which is connected to the suction line 3. Furthermore, the suction fluid regulator 22 is flow- connected to a suction fluid collection container 23, which in the present case is also contained in the console 1. In this case, it can also be provided that the suction fluid collection container 23 is designed at least partially separate from the console 1 and connected by a line. The suction fluid regulator 22 sets the flow rate and / or the negative pressure of the suction fluid in the suction line 3. The suction fluid regulator 22 is also communicatively connected to and controlled by the control unit 8. The control unit 8 is designed in such a way that the pressure in the capsular bag can be maintained substantially constant during the treatment of the eye 9.

[0047] The console 1 also comprises a generator unit 15 for providing a time-varying electrical drive signal for the electrical drive unit 10 of the handpiece 2. In the present case, the electrical drive signal is formed by an AC voltage, the frequency of which can be set in the range of approximately 10 kHz to approximately 80 kHz. Preferably, the frequency is approximately 40 kHz. Depending on the power setting of the treatment, the amplitude of the AC voltage can be in the range of approximately 0 V to approximately 1000 V, for example approximately 300 V. The generator unit 15 is detachably connected to the electrical line 11, so that the AC voltage can be applied to the electrical drive unit 10 during the intended operation. Depending on the application of the AC voltage, the treatment needle 6 is mechanically excited to oscillate, so that the desired treatment of the eye 9, in particular of the eye lens 13, can be carried out. In the present case, the operation of the generator unit 15 can also be controlled by the control unit 8, for which purpose the generator unit 15 is communicatively connected to the control unit 8. Thus, for example, the control unit 8 can control the operation of the handpiece 2, in particular of the treatment needle 6. For example, the frequency, the amplitude, etc. can be set by the generator unit 15 generating an appropriate amount of AC voltage. In this way, a mechanical power of up to approximately 50 W can be provided on the oscillating needle tip 7 for the treatment. As a rule, this mechanical power is sufficient to emulsify even particularly hard cataracts.

[0048] During the treatment, an undesired strong heat build-up can occur, not only but especially in the region of the cornea 12 of the eye 9. In this case, the heat build-up can be so strong that the cornea 12 is damaged, for example, resulting in a burn. This can cause permanent damage. Therefore, it is desirable to keep the unnecessary heat input as small as possible. In particular, the longitudinal oscillation of the treatment needle 2 can also generate forces that counteract the suction-like suction effect in the region of the needle tip 7. This can cause particles or lens fragments that should be flushed in the suction range to be pushed away. Therefore, this can result in a longer duration of the operation and an increased total energy input into the eye 9.

[0049] In this context, by means of the present application, in particular by making the oscillation operation of the treatment needle 6 dependent on the contact with the particles 19 or lens fragments, a significant improvement can be achieved. Outside the contact, the treatment needle 2 does not need to be driven by means of oscillation.

[0050] For this purpose, the drive unit 10 is used in a similar way to the sensor unit. Therefore, the control console 1 also comprises a detection unit 16, which is likewise connected to the electrical line 11. Thereby, the detection unit 16 is connected to the electrical line 11 in order to be connected in parallel to the generator unit 15. The detection unit 16 is also in communication connection with the control unit 8, in particular with the evaluation unit 17 of the control unit 8. By means of the detection unit 16, an electrical contact signal 35 from the electrical drive unit 10 on the electrical line 11 can be detected when the particles 19 contact the treatment needle 6. For this purpose, the generator unit 15 is deactivated during the detection, so that it does not output any drive signal 36 to the electrical drive unit 10. Therefore, in the non-oscillating or low-oscillating state of the treatment needle 6, in particular, an electrical contact signal 35 from the electrical drive unit 10 can be detected by means of the detection unit 16. The detected electrical signal 35 can then be evaluated by means of the evaluation unit 17, so that a contact of the particles 19 with the treatment needle 6 can be determined on the basis of the evaluation. Therefore, the control unit 8 obtains information about when the treatment needle 6 contacts any particles or lens fragments.

[0051] In principle, therefore, two operating states can be distinguished during the treatment. In a first operating state, the ultrasonic energy is used to pulverize or emulsify the eye lens 13. In this operating state, the treatment needle 6 or the needle tip 7 is at least partially in contact with the eye lens 13. Therefore, in this operating state, the ultrasonic energy should be output directly and preferably without delay from the treatment needle 6 to the eye lens 13. In a second operating state, the ultrasonic energy cannot be used to pulverize or emulsify the eye lens 13, since there is no contact between the treatment needle 6, in particular the needle tip 7, and the eye lens 13. In order to keep the ultrasonic energy output as small as possible and / or to avoid pushing away particles 19 or lens fragments to be flushed in this operating state, the ultrasonic energy output should be stopped or at least reduced. Therefore, it is advantageous to detect the switching between the two operating states as quickly as possible.

[0052] Furthermore, at the first signs of a clogging, the suction force should be increased by increasing the negative pressure in the suction line 3. Preferably, the output of the ultrasonic energy should be started or increased at least synchronously therewith. Thereby, it is possible to achieve that the particles 19 stay directly on the vibrating tip 7 and the comminution or emulsification can be carried out very quickly. Thereby, the comminution time can be shortened and thus the amount of heat input into the eye 9 can be significantly reduced. By increasing the suction force, it is also possible to avoid a situation in which the particles 19 are pushed away from the tip 7 by the ultrasonic energy, so that the treatment duration can also be reduced.

[0053] Figure 3 A schematic block diagram showing a possible schematic structure of the detection unit 16 and the evaluation unit 17 for implementing the present application is shown. The present application is based, inter alia, on the detection of the electrical contact signal 35 in a state of the treatment tip 6 without or with low oscillation.

[0054] Thus, in the detection state, the generator unit 15 is deactivated and does not supply any drive signal 36 to the electrical drive unit 10 of the handpiece 2. Thereafter, i.e. preferably after the decay of the oscillation state of the treatment tip 6 caused by the electrical drive unit 10, the detection unit 15 can use the electrical drive unit 10 in a sensor-like manner. If a particle 19 comes into contact with the treatment tip 6, a force acts on the piezoelectric element of the electrical drive unit 10, as a result of which a voltage is generated due to the piezoelectric effect, which can be tapped at the electrodes in contact with the piezoelectric element and thus on the entire electrical line 11. It is noted that no separate piezoelectric element is designed as a sensor; rather, all piezoelectric elements of the handpiece 2 are used as sensors. The curve of this voltage is depicted in Fig. 3 as the electrical contact signal 35. This voltage can be detected via the electrical line 11 and the detection unit 16 and can be evaluated by means of the evaluation unit 17. This will be explained in the following. Furthermore, it is assumed in the present case that the deactivation of the generator unit 15 does not result in an attenuation or substantial attenuation of the electrical contact signal 35 generated by the electrical drive unit 10 in this operating state due to the generator unit 15. Alternatively, the generator unit 15 can be designed appropriately for this purpose. Figure 4

[0055] ​The detection unit 16 comprises an amplifier 24 as well as a first comparator 25 and a second comparator 26. The amplifier 24 as well as the first comparator 25 and the second comparator 26 are also connected to a digital signal processing unit 29 of the evaluation unit 17, which provides the amplifier 24 as well as the first comparator 25 and the second comparator 26 with suitable operating parameters, as explained below. On the input side, the amplifier 24 is connected to the electrical line 11. In the present case, the amplifier 24 serves as a linear amplifier and amplifies the electrical contact signal 35. The amplified electrical contact signal 35 is then provided to an analog-digital converter 28 of the evaluation unit 17. Furthermore, on the input side, the first comparator 25 is also connected to the electrical line 11. The first comparator 25 compares the signal on the electrical line 11 with a first comparison value. The first comparison value is chosen in such a way that the operation of the generator unit 15 can be reliably detected. The amplifier 24 has a corresponding overload capability design. Thus, it can be determined by means of the output signal of the first comparator 25 whether the generator unit 15 is activated. The corresponding output signal is provided to the evaluation unit 17 via a comparison data supply 27. Furthermore, on the input side, the second comparator 26 is connected to the output of the amplifier 24. The second comparator 26 compares the output signal of the amplifier 24 with a second comparison value, which is chosen in such a way that the electrical contact signal 35 can be reliably detected with respect to interference signals. The corresponding comparison result is likewise provided to the evaluation unit 17 via the comparison data supply 27. Thus, the evaluation unit 17 can obtain information about whether the electrical contact signal 35 is present.

[0056] The evaluation unit 17 comprises a digital signal processing unit 29 which is connected to both the analog-digital converter 28 and the comparison data supply 27. The digital signal processing unit 29 processes the corresponding signals and determines when the electrical contact signal 35 is present and its characteristics. Furthermore, the digital signal processing unit 29 is connected to a system control unit 30 of the control unit 8, by means of which system control unit system information is provided to the digital signal processing unit 29. The system control unit 30 can comprise a database or the like, for example. Furthermore, the digital signal processing unit 29 also provides parameters for the amplifier 24, such as a gain factor or the like, and a first comparison value and a second comparison value for the first comparator 25 and the second comparator 26, respectively. Thus, the detection unit 16 can be set as required during the intended operation in order to reliably determine the contact of the particle 19 with the treatment needle 6. By means of the digital signal processing unit 29, appropriate control signals can be provided for an ultrasonic power control unit 31 and an ultrasonic mode unit 32. The ultrasonic power of the generator unit 15 can be set by means of the ultrasonic power control unit 31. Furthermore, the pulse pattern of the ultrasonic power which the generator unit 15 is intended to provide can be set by means of the ultrasonic mode unit 32. Both units are likewise connected to the generator unit 15. Furthermore, the digital signal processing unit 29 provides appropriate data for a contact determination unit 33. On the basis of the data provided by the digital signal processing unit 29, the contact determination unit 33 determines whether a contact between the particle 19 and the treatment needle 6 is present. This output signal can also be provided to the generator unit 15, for example in order to activate the output of the ultrasonic power or the electrical drive signal 36.

[0057] Furthermore, the digital signal processing unit 29 provides data to a fluid control unit 34, which provides appropriate control signals to the irrigation fluid regulator 20 and the aspiration fluid regulator 22. Thus, for example, the pressure and / or flow conditions in the irrigation line 4 and the aspiration line 3 can be appropriately set, so that as reliable and successful a treatment as possible can be achieved. This can include, for example, an increase in the negative pressure in the aspiration line 3 in the event of a detected occlusion. The digital signal processing unit 29 can evaluate the electrical contact signal 35, for example, with respect to the amplitude, frequency, decay behavior, etc., in order to calculate further data therefrom, for example, for the units 31 to 34. In the present example, the evaluation unit 17 comprises an appropriately programmed computer unit. It goes without saying that, for this purpose, appropriate hardware circuits or combinations with computer units can also be provided in alternative configurations. In certain cases, depending on the configuration, an amplifier 24 can also not be used in alternative exemplary embodiments. The digital signal processing unit 29 can further comprise one or more digital filters, pattern recognition, contact classification, etc. The digital signal processing unit 29 can also provide a system observation, in which it can be assumed that, when no contact between the particle 19 and the treatment needle 6 is determined, there is also typically no particle 19 or lens fragment in the region of the treatment needle 6. The output of the ultrasound energy can thus be reduced or even terminated. This can reduce the heat input into the eye 9, in particular into the region of the incision. Conversely, if a contact is detected, the ultrasound energy can be activated or automatically increased, so that emulsification can take place. Furthermore, other states or properties of the particle 19, for example, the size, hardness or velocity, can also be detected or determined, so that it can be determined, for example, by observation over time, whether the activation, deactivation, increase or decrease of the ultrasound energy output can be advantageously provided, or a particular pulse pattern is applied during the ultrasound output. In an advantageous configuration, it can be provided to start with a higher ultrasound energy output and then to reduce it over time.

[0058] The functionality of the present application will also be based on Figure 4The depicted diagram is to be interpreted such that it shows a voltage curve over the electrical line 11. The abscissa represents time, the ordinate represents voltage. Obviously, there is no drive signal 36 before the time of contact 37. At this time, the ultrasonic energy output due to the activation of the generator unit 15 is deactivated. Therefore, the drive signal 36 is essentially close to zero. The particle 19 contacts the treatment needle 6 at the time of contact 37. Since the generator unit 15 does not substantially attenuate the electrical contact signal 35 present on the electrical line 11, the detection unit 16 is able to detect the voltage of the contact signal 35. This is depicted by the short pulse starting at the time 370 after the time of contact 37. The amplitude A2 of the electrical contact signal 35 is smaller than the amplitude A3 of the drive signal 36. The amplitude A2 is preferably not more than 90%, preferably not more than 50% and particularly preferably not more than 30% of the amplitude A3 of the drive signal 36. Preferably, the amplitude A2 is at least twice the amplitude Al of the system oscillation noise 50 representing a low oscillation state. Thus, the amplitude A2 of the electrical contact signal 35 can be clearly distinguished from the amplitude Al of the system oscillation noise 50. The first comparator 25 and the second comparator 26 serve this purpose; by their digital values, they assist the digital signal processing unit 29 in the contact determination. The digital signal processing unit 29 allows an evaluation of the detected electrical contact signal 35 so that the generator unit 15 can be activated to output the electrical drive signal. This is implemented directly after the detection of the electrical contact signal 35. For the Figure 4 With the shown time resolution, the start of the drive signal almost coincides with the start of the contact signal 35, therefore, for the sake of clarity, Figure 4 the electrical drive signal is not shown in the diagram. However, Figure 4 the start of the electrical drive signal 36 is shown when using the conventional method before, in which a clogging on the needle tip 7 is detected. This drive signal 36 starts at the start time 39, which is delayed by a time interval 38 compared to the start of the drive signal according to the application, wherein the time interval 38 can be approximately 80 ms. In any case, it is possible with the application that the electrical drive signal can be activated automatically in time after the contact of the particle 19 with the treatment needle 6, so that emulsification is achieved. Thus, the application allows a control of the ultrasonic energy input into the eye 9 in an automatic or at least partially automatic manner, so that the total heat input can be reduced.

[0059] Figures 5 to 8 The contact between the particle 19 and the treatment needle 6 can be implemented as shown by the schematic drawing. In Figures 6 to 7 in the diagram, the treatment needle 6 is excited longitudinally; this is indicated by the arrow 18 in the longitudinal extension direction of the treatment needle 6. Figure 5 The diagram shows the case in which the particle 19 still maintains a small distance to the treatment needle 6. In this state, the ultrasonic energy output is preferably still in the deactivated state. Figure 6A partial occlusion is shown, in which the particle 19 partially occludes the opening of the suction line 3. As explained above, this contact can be determined, so that the ultrasonic energy output can be activated automatically, so that the particle 19 can be emulsified. The same operation can also be carried out Figure 7 in the case shown, in which the particle 19 completely occludes. In this case, too, the contact can be determined and the ultrasonic energy output can be activated automatically, so that the particle can be emulsified. In contrast, Figure 8 A situation is shown in which the treatment needle 6 is excited to oscillate transversely as a result of the transverse contact of the particle 19 with the treatment needle 6. This, too, can be determined by the application and the ultrasonic energy output can therefore also be activated automatically.

[0060] In another configuration, it can also be additionally provided that, when there is no occlusion, the ultrasonic energy output can be deactivated automatically by a further system observation, for example as disclosed in US 9,144,517. The disclosure of this US patent should be considered to be included in the present application. Thus, an almost fully automatic ultrasonic energy provision can be controlled, so that the ultrasonic energy is only provided when it is necessary to advance the treatment. For this, too, it can be considered, for example, to change the flow in the suction line 3. For example, as Figure 5 depicted, if a change in the flow in the suction line 3 is detected before the particle 19 comes into contact with the needle tip 7, it can be provided, for example, that the ultrasonic output is activated even if the contact has not yet occurred. If the contact occurs, the power can be increased. Furthermore, in another configuration, it can be provided that, in the case of a determined contact and the deactivation of the drive signal 36, the negative pressure in the suction line 3 is first increased in a first step. Only when a sufficient occlusion is determined, the ultrasonic output is activated in a second step. In this case, the use of the application thus results in that in the first step only the suction fluid regulator 22 is initially acted upon. Only in the second step, the generator unit 15 is then acted upon.

[0061] The present application can achieve the following advantages: By faster detection and determination of the contact of the particles 19 with the treatment needle 6, an optimized activation of the ultrasound power can be achieved. In this case, the sensor system can be arranged in the handpiece 2, without having to be arranged in the pump of the control console 1, as in the case of a detection of the blockage based on a change in pressure and / or flow, for example at a distance of two meters, wherein the corresponding tube connections can have interactions, in particular thus resulting in a dead time in the measurement path, which can be for example 60 to 70 ms. Due to the faster activation of the ultrasound output, the equivalent phacoemulsification time (EPT) or the treatment duration can be reduced, in fact, the ultrasound output takes place almost immediately when needed. Further, due to the faster increase of the negative pressure in the aspiration line 3 in the case of contact, the aspiration particles can remain longer on the tip 7 of the treatment needle 6, so that an efficiency can be achieved and the EPT or the heat input can be reduced. The present application allows the use of ultrasound energy based on particle contact, instead of relying on conventional blockage detection. The particle contact on the outside or the end face of the treatment needle 6 can be detected. Thus, the ultrasound energy can be provided when the treatment needle 6 is twisted and / or moved laterally, and the reliability of the contact detection can be increased in the engraving phase of the grooves on the eye lens 13. In contrast, the prior art only provides a blockage detection based on a change in flow, wherein the particles 19 cause a change in the flow of the aspiration fluid or are located in the flow path.

[0062] A further application of the event-based ultrasound energy supply can be in combination with the current fluid blockage detection. For example, as shown in Figure 5 the case of a particle 19 advantageously located in front of the outlet opening of the aspiration line 3, but not yet in mechanical contact with the treatment needle 6, the fluid blockage detection can be used to trigger the ultrasound activation. The loss of contact can also be detected in the same way. Furthermore, with the present application additional trigger events related to the contact of the particles 19 with the treatment needle 6 can be determined, for example, whether the particles 19 contact the end face or the outside of the treatment needle 6. The present application enables a fast contact detection. At the same time, the present application can be implemented with little outlay, in particular at low cost. There is no need to modify the handpiece.

[0063] Figure 9 The advantages of the present application over the prior art are compared again. For this purpose, Figure 9 six time-synchronized signal diagrams 40 to 45 are shown, whose abscissae each represent the time and whose ordinates each represent the voltage as a signal value. With regard to the abscissa, the diagrams are divided into a region A and a region B. Region A relates to the case depicted based on Figures 5 to 7 Region B relates to the case depicted based on Figure 8 .

[0064] Fig. 40 and Fig. 41 relate to the application of the present application. The signal diagram 40 shows the contact detection according to the present application, in particular an end surface contact on the tip 7 in the area A of the signal diagram and a lateral contact transverse to the longitudinal extension of the treatment needle 6 in the area B of the signal diagram. It is apparent from the signal diagram 40 and Fig. 41 that, according to the present application, the electrical drive signal 36 in the form of an ultrasound pulse 47 can be output almost immediately after the contact is determined at time 37. This applies both to the end surface contact and to the lateral contact. Fig. 42 and Fig. 43 show the corresponding case of the prior art. As depicted on the basis of the diagram 42, it is apparent that, in the area A, the detection of the occlusion is subject to a considerable delay, as indicated by the graph 48. As depicted in the diagram 43, the output of the electrical drive signal in the form of an ultrasound pulse 49 is implemented with a corresponding delay. Furthermore, in the case of a lateral contact transverse to the longitudinal extension of the treatment needle 6, no ultrasound pulse 49 is output. This case cannot therefore be reliably identified in the prior art. Fig. 44 and Fig. 45 even more clearly reveal the advantages brought about by the use of the present application. Fig. 44 depicts the electrical signal 35 captured by the present application for the areas A and B. In comparison with the prior art, it is apparent from the area A according to Fig. 45 that the reaction time of the present application is shorter, which is marked in Fig. 45 by the time interval 38. In the case of a lateral contact transverse to the longitudinal extension of the treatment needle 6 in the area B, the prior art does not provide any reaction in comparison with the present application.

[0065] Figure 10 A schematic diagram of a voltage / time curve is shown. In this case, the output of the drive signal 36 is deactivated. In this case, the voltage on the electrical line 11 is also depicted. At time 37, the particle 19 comes into contact with the treatment needle 6. As a result, the latter is excited to oscillate, and this generates a damped AC voltage by the drive unit 10 as an electrical contact signal 35. This signal can be detected by the detection unit 16 and can thus be provided to the evaluation unit 17. It is apparent that the oscillation amplitude of the electrical contact signal 35 depicted here is approximately 80% of the amplitude of the drive signal 36; see also Figure 4 The detection unit 16 therefore has a corresponding design such that it does not enter an overload state as a result of the drive signal 36.

[0066] The exemplary embodiments are merely intended to explain the present application and are not intended to limit the present application.

Claims

1. A console (1) of an ophthalmic surgical system (100) for operating an ophthalmic surgical handpiece (2) which is connectable to the console (1) and comprises a treatment needle (6) and an electrical drive unit (10) for driving the treatment needle (6) by oscillation, wherein the console (1) comprises at least one generator unit (15) for providing a time-varying electrical drive signal for the electrical drive unit (10), a detection unit (16) electrically coupled to the electrical drive unit (10), wherein the detection unit (16) is adapted to detect an electrical contact signal (35) of the electrical drive unit (10) based on a second oscillation amplitude (A2) in a low oscillation state of the treatment needle (6) in which the treatment needle oscillates with a maximum first oscillation amplitude (Al), and wherein the generator unit (15) is designed to provide the drive signal in such a way that the electrical drive unit (10) is deactivated during the low oscillation state, and an evaluation unit (17) for evaluating the detected electrical contact signal (35) and determining a contact of a particle (19) with the treatment needle (6) based on the evaluation, characterized in that the detection unit (16) is adapted to detect the contact signal when the second oscillation amplitude (A2) is greater than the first oscillation amplitude (Al).

2. The console of claim 1, characterized in that the generator unit (15) and the detection unit (16) are electrically connected in parallel on one side of the electrical drive unit.

3. The console of any one of claims 1 or 2, characterized in that the console is configured such that: the detection of the electrical contact signal (35) by the detection unit (16) is activated only after expiration of a specified time interval starting at a time instant at which the electrical drive signal ends.

4. The console of claim 3, characterized in that the console is configured such that: the time interval is determined based on a mechanical damping of the oscillation of the treatment needle (6).

5. The console of any one of claims 1 or 2, characterized in that the console is configured such that: a size, a hardness or a velocity of the particle (19) is determined based on the evaluation of the electrical contact signal (35) by the evaluation unit (17).

6. The console of any one of claims 1 or 2, characterized in that the console is configured such that: the detection of the electrical contact signal (35) by the detection unit (16) is deactivated when the generator unit (15) is activated to output the electrical drive signal.

7. The console of any one of claims 1 or 2, characterized in that the console is configured such that: the generator unit (15) is activated to output the electrical drive signal after the contact of the particle (19) with the treatment needle (6) is determined by the evaluation unit (17).

8. An ophthalmic surgical system (100) for treating an eye (9), the ophthalmic surgical system having at least: ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ ​ - an ophthalmic surgical handpiece (2) for operating on an eye lens (13), comprising a treatment needle (6) and an electrical drive unit (10) for driving the treatment needle (6) by oscillation, and - a control console (1) for operating the ophthalmic surgical handpiece (2), the ophthalmic surgical handpiece (2) being connectable to the control console at least during intended operation, and the control console comprising a generator unit (15) which is couplable to the ophthalmic surgical handpiece (2) and which is for providing a time-varying electrical drive signal for the electrical drive unit (10) of the ophthalmic surgical handpiece (2), characterized in that the control console (1) is designed in accordance with any one of the preceding claims.

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