High voltage pulse power driver

Abstract: The invention provides a relatively simple high voltage pulse power driver which is particularly useful for ultrasound medical imaging systems to provide a controlled amplitude power burst to a piezoelectric transducer element. The circuit according to the invention comprises: a high voltage power source, a variable low voltage power source (V pc ) means to receive incoming pulses (33) having a fixed low potential; means for generating a control voltage comprising comparator means (34) to compare said received pulses with said variable low voltage power source and to clamp said received pulses at the level of potential of said variable power source; converter means (36) to convert said control voltage to a control current, wherein the amplitude of said control current is directly proportional to the amplitude of said control voltage and to feed said pulsed controlled current to an output stage comprising: coupling means (38, 31) for coupling said control current to said high voltage source and to said load for applying said pulses to said load in response to switching states controlled by said control current; and means (40) to limit the current from said high voltage source to said load.

Description: The invention relates to an ultrasound imaging system comprising an array of transducer elements and a transmit stage with a plurality of high voltage pulse power drivers, each driver being adapted to be connected to a high voltage power source and to supply a variable power drive to at least one of the transducer elements. A typical ultrasound imaging system used for medical imaging includes at least one ultrasound transducer, usually in the form of an array of transducer elements. The transducer is usually connected to transmitter stage circuitry, receiver stage circuitry and whatever devices may be necessary to effect mechanical scanning of the transducer. The transmitter stage comprises a generator of electrical excitation signals which are sent to the transducer. The transducer converts these signals into periodic pulse trains of ultrasound mechanical energy. Transducer arrays used in medical imaging systems come in many forms, such as linear arrays, phased arrays, annular arrays and collimated image arrays. A transducer array usually consists of a plurality of transducer elements disposed on a surface in some designed arrangement such as a row, matrix or other geometric pattern. The individual elements or groups of elements are actuated or pulsed in sequence to transmit a beam of ultrasound energy at a field of interest. Ultrasound echoes are returned from the target and may be received on the same transducer elements. The pulse echo data received is then interpreted and displayed to produce an image. A transducer may be apodized by shaping the distribution of energy applied across the transducer to a desired aperture function. For a single disc, piezoelectric transducer, this has been accomplished by shaping the applied electric field through use of different electrode geometries on opposite sides of the disc as described, for example, in Martin and Breazeale "A Simple Way to Eliminate Diffraction Lobes Emitted by Ultrasonic Transducers", J. Acoust. Soc. Am. 49 No. 5 (1971) 1668, 1669 or by applying different levels of electrical excitation to adjacent transducer elements in an array. However the method of Martin and Breazeale is limited to a number of simple fixed aperture functions and the use of separate surface electrodes requires complex transducer geometries and/or switching circuits. Precise control of the potential fed to each transducer element of an array is essential for apodization in the transmit stage of a pulse echo imaging system. Ultrasound transmitters in present use are of the kind known as "voltage mode drivers". Typically an ultrasound transducer element is connected via a solid state switch to a fixed, high voltage supply. During transmission, the switch is closed for a short time, or in a repetitive manner, to produce a series of pulses across the transducer. The amplitude of these pulses is related to the voltage level of the supply and can only be controlled by changing the power supply potential. For an application that employs a linear array transducer of more than 100 elements, especially a shifting array, the precise control of this low impedance potential would necessitate a tremendous increase in complexity since each transducer element driver would require a separate controllable (voltage) supply. It is an object of the present invention to provide a reletively simple circuit which solves the problem of providing a variable voltage level to each transducer element in an array. The ultrasound imaging system according to the invention is characterized in that at least one of the pulse power drivers comprises: a variable low voltage power source; means to receive incoming pulses having a fixed low potential; comparator means to compare said received pulses with said variable low voltage power source and to clamp said received pulses at the level of potential of said variable power source, said clamped pulses forming a control voltage; converter means to convert said control voltage to a control current, wherein the amplitude of said control current is directly proportional to the amplitude of said control voltage and to feed said pulsed control current to an output stage comprising: coupling means comprising a transistor means forming a cascode configuration with said converter means, said coupling means controlling a current drawn from said high voltage power source through a load comprising at least one of the transducer elements such that the amplitude of said low voltage power source controls the amplitude of the current from said high voltage source through said load. In this new driver circuit, the switching devices do not saturate, rather they drive a controlled amount of current into the transducer element. In addition to facilitating a simpler design, the new approach allows a much faster control of the pulse amplitude. A preferred embodiment of the circuit according to the invention is characterized in that the converter means comprise a current gain transistor, the base of said current gain transistor receiving said control voltage and a cascade of current amplifying transistors being connected to the emitter and collector of said current gain transistor; the coupling means comprising a FET source by said current amplifiers, the drain of said transistor being connected to said load, whereby current is drawn from said high voltage source through said transistor and said load. It is to be noted that US-A-4 528 520 discloses a wide band high output amplifier suitable as a driving circuit for a cathode ray tube display. This circuit comprises a cascode configuration of a bipolar transistor and a FET. It is further noted that the book 'Sourcebook of Electronic Circuits' by J. Markus, McGraw-Hill Book Company, 1968, page 330 discloses a circuit called 'Video Signal Processor' in which an incoming video signal is compared to a threshold level and a limit level, said levels being percentages of the incoming video signal. Preferably, the circuit according to the invention operates as a push-pull power driver. untii turned on by pulses on its inputs, the driver circuit draws no power. A variable potential, V pc , is applied to each of two active clamps. These clamps monitor the magnitude of the potential on the input lines relative to the control potential, V pc . When complementary bursts of clock pulses are applied to the two inputs of the driver, the potential at the base of each drive transistor rises toward that potential. When an input line reaches a potential equal to V pc + V be , a clipping transistor circuit turns on and draws sufficient current to hold the drive potential at V pc + V be . As a consequence, this is the level of drive potential applied to the base of the associated complementary output stage. The total current conducted by this output stage is set by the magnitude of the clipped drive signal and the magnitude of a resistor in the emitter circuit, which returns the total current to the circuit common. Thus, the amplitude of V pc controls the amplitude of the output current which flows through parallel current amplifying arrangements between the input stages and output stages and the load. This output current of the driver circuit is directly proportional to the V pc input potential. At the trailing edge of each pulse there is a fast return to the off condition. The driver of the present invention operates in a non-saturating current mode in which the switching devices drive a controlled amount of power into the transducer element, allowing very fast control of pulse amplitude. In particular, the pulsed current driver enables shaping of the power across the full transmit aperture of many electrical transducers, thus controlling the beam width. The circuits all operate from a single fixed high voltage power supply to provide a profile of output power. The output is independent of variations in the high voltage power supply, thus achieving ripple-free output. These features are particularly useful for focusing and apodization at the transmit stage of a pulse echo imaging system. The invention will now be explained in detail with reference to the drawings. Figure 1 is a simplified partial block diagram of the "front end" of a pulse echo ultrasound imaging system showing the interconnection of the subsystems relevant to the present invention. Figure 2 is a block diagram of the driver circuit of the present invention. Figure 3 is a simplified circuit diagram of a present embodiment of the high voltage pulse power driver of the invention. Figure 4 is a detailed circuit diagram of the driver of Figure 2. The present invention may be used with associated circuits for transmitting an apodized and focused beam of coherent ultrasound, utulizing an array of ultrasound transducers, accomplishing precisely timed delays and capable of coherent pulse trains over a wide range of burst lengths. A transducer array for pulse echo ultrasound imaging is apodized by causing the transmit output pulse magnitude to vary as a function of its position in the transmitting aperture. The desirability of apodization and the difficulty of achieving apodization with a shifting aperture are the reason for the present invention. The invention will be described in the context of a system for ultrasound medical imaging, and specifically in terms of digitally controlling a linear array of transducer elements to transmit an apodized and focused wavefront of ultrasound energy. A transmit focus circuit and an apodization profiling circuit have been disclosed in the cross-referenced applications which are incorporated herein by reference. Turning now to the drawings, Figure 1 is a simplified block drawing of the "front end" of an ultrasound medical imaging system which incorporates the present invention. In this imaging system, a linear transducer array 16, having N transducer elements 16a,...,16n, is connected to both a transmit stage 10 and a receive stage 18. The transmit stage 10 has N driver circuits 14a, ...,14n and N transmit focus blocks 12a, ..., 12n and the receive stage 18 has a display system 19. In this particular system the parameters for the generation of each line scan are precalculated and stored in a system memory included in a control unit 20. The parameters for apodization are likewise precalculated and stored. Prior to the generation of each line scan, the type of line scan and the specific parameters for that scan are selected. The present invention is directed to a high voltage pulse power driver which provides a controlled amount of power to the drivers of the transducer elements. A variable current supplied to each driver is directly proportional to a variable control voltage from an opodization profiling circuit(also included in the control unit 20) in which selected parameters enable a subset of elements in an array 16 of N transducer elements to transmit an opodized focused beam of coherent ultrasound, thus generating a focused wavefront. The invention may be used with an aperture profiling circuit such as that disclosed in EP-A 0 302 554 whereby typically the transducer elements in an aperture each receive a calculated percentage, V pc , of the reference voltage V r , according to the profile of potential shown in that application. Figure 2 is a block diagram which illustrates the principle of the present invention. The driver circuit 14i of the present invention uses a fixed high voltage power source to supply a variable power drive to piezoelectric transducer elements wherein the variable driver 14i is controlled by a low potential control signal. In Figure 2, the variable high voltage power is applied to the transducer 16i through a transformer 31. The low potential is supplied by a variable power control, V pc , that determines the driver magnitude and originates from the apodization circuit described in the EP-A 0 302 554. The control signal V pc is applied to the input clamp circuit 32. When the drive pulse train 33 of fixed amplitude is applied, the potential rises to the amplitude of the control signal V pc and it is clipped above that level. The input signal is clipped at V pc + V be . The resulting low voltage is outputted via a comparator 34 to a voltage-to-current converter 36 whose output serves to control the high voltage current via a control circuit 38. The total current conducted by the output stage is set by the magnitude of the applied signal and the magnitude of a current sensor resistor 40 in the emitter circuit of the current converter 36. The amplitude of V pc , therefore, controls the amplitude of the output current to the load 31. Figure 3 is a simplified circuit ambodying the invention. In the circuit of Figure 3, a pulse train 33 is applied to the input of the driver. The potential at the base of the drive transistor Q2A rises toward the potential of the pulses. When the potential on the base reaches V pc + V be , the clipping transistor circuit Q1A and Q1B turns on and draws sufficient current to hold the drive potential at V pc + V be . As a consequence, this is the level of drive potential applied to the base of the output stage Q2A. Q3 serves as the high voltage current control. In Figure 3, a resistor R3 senses the total current conducted by the output stage. The output current is directly proportional to V pc . The constant of proportionality is set by the sense resistor R3. The load represented by Transformer T in Figure 3 could be a resistor or a non-center-tapped transformer. The precise electrical embodiment of the load is not part of the invention. Transistor Q1 is compounded as Q1A and Q1B to reduce the loading of V pc . Q2 is compounded as Q2A and Q2B to reduce loading of the drive. Both are in complementary Darlington circuits. The stages are complementary to avoid summing base-emitter junctions. Q2B is created from four parallel transistors to limit the collector currents of each transistor to provide a reasonable current gain. Figure 4 is a circuit diagram of a preferred embodiment of the high voltage pulse power driver 14i of the present invention. The circuit for driver 14i operates as a push-pull power driver using a center tapped transformer coupler 102. The purpose of driver circuit 14i is to use a fixed high voltage source to supply a variable power drive to a piezoelectric transducer element 16i under the control of a low voltage control signal V pc . The control signal V pc enables the circuit to change a pulsed voltage source to a pulsed current output such that the amplitude of the voltage pulses controls the amplitude of the current pulses. Since the driver is a push-pull driver, it requires two complementary bursts of pulses, one burst delayed by one-half cycle, and converts these bursts in parallel circuits. The inputs to driver circuit 14i are two complementary bursts of pulses, on input lines B0A and B0B, which are outputted from a clock pulse generator circuit, such as the transmit focus block 12i (see figure 1). Driver circuit 14i is sourced from a variable control voltage, V pc , which, in the preferred embodiment, is outputted from the apodization profiling circuit of the EP-A 0 302 554. When complementary bursts, burst 33(i) on line B0A and burst 33(2) on line B0B, of clock pulses of fixed amplitude are applied to the input of driver 14i, the potential at the base of drive transistors Q3, Q4 rises to the amplitude of the control signal V pc . The control signal V pc is applied to the input clamps 104,106. When each line reaches a potential equal to V pc + V be , the clipping transistor circuits 104, 106 turn on and draw sufficient current to hold the drive potential at V pc + V be . As a consequence this is the level of drive potential applied to the base of the complementary output stage Q13, Q14. Thus,the drive potential remains at the level set by the variable power control output of the apodization circuit. The amplitude of V pc varies from one driver circuit to another according to the profile of potential applied across the elements of a transducer array for a desired aperture function. A high voltage power supply 108 which is applied to the primary winding of transformer 102, allows the voltage to build up on resistors R3, R4 which are connected to ground, through current flowing in the circuit. The base-to-emitter current on Q3, Q4 then appears on their collectors. This current then turns on the cascade arrangements Q5 through Q8 and Q9 through Q12, which, in turn, turn on Q13 and Q14. The cascaded transistors Q5-Q8 and Q9-Q12 are current amplifiers which increase the current gain from the base of Q3, Q4 to the base of Q13, Q14. With Q13, Q14 alternatively turned on, current is drawn through transformer 102 from the high voltage power supply 108 of 100V and is controlled by Q13, Q14 stabilizing the voltage across R3, R4, which will adjust Q3, Q4 when the applied voltage is not balanced. The voltage across R3 or R4 equals the voltage at the bases of Q3 and Q4 minus the base-emitter drop, therefore V pc . The voltage across R3, R4 then sets the amount of current through transformer 102. As V pc varies, the controlled current will vary in proportion. Thus V pc sets the currents that flow through the current gain arrangements via Q13, Q14, transformer 102 and the load. Q13, Q14 are power amplifiers. The output current is controlled by V pc and it is given by Iload = V pc + V be - V be R3 or V pc + V be - V be R4 = V pc R where R3 = R4 = R. The resistors R17, R18 and capacitor C2 decouple Q13 from Q14 to prevent oscillation. R15, R16 are sized to prevent damage to Q13, Q14 in case leakage through Q13, Q14 is larger than the leakage through the current amplifiers, in which case the source potential may rise above the gate potential sufficiently enough to cause breakdown. Transformer 102 has high self-inductance and does not cause significant loss. R19 in parallel with the transducer element 16i causes a fast return to base-line at the trailing edge of each pulse. Alternative embodiments may be utilized. Q13, Q14 can be replaced by high voltage Darlingtons. The parallel combinations of Q5-Q8 and Q9-Q12 could be replaced by a single power rf transistor. The combination could also be replaced by a single channel power MOS transistor, in which case the upper frequency of operation might be compromised because of the high input capacitance of this device. Also a higher gate-to-bias ratio would be required for Q13, Q14. The winding ratios of transformer 102 can be adapted to suit other load impedances. Thus, the circuit of the present invention can provide a controlled amplitude, power burst across a low impedance transducer element. It achieves this in a non-saturating current mode operation in which the switching devices drive a controlled amount of power into the transducer element. This circuit permits of very fast control of pulse amplitude in a very simple design.

Claims: An ultrasound imaging system comprising an array (16) of transducer elements (16i) and a transmit stage (10) with a plurality of high voltage pulse power drivers (14i), each driver being adapted to be connected to a high voltage power source (HV) and to supply a variable power drive to at least one of the transducer elements, characterized in that at least one of the pulse power drivers (14i) comprises: a variable low voltage power source (V PC ); means to receive incoming pulses (33) having a fixed low potential; comparator means (32) to compare said received pulses (33) with said variable low voltage power source (V PC ) and to clamp said received pulses at the level of potential of said variable power source, said clamped pulses forming a control voltage; converter means (36) to convert said control voltage to a control current, wherein the amplitude of said control current is directly proportional to the amplitude of said control voltage and to feed said pulsed control current to an output stage comprising: coupling means (Q3) comprising a transistor means forming a cascode configuration with said converter means, said coupling means controlling a current drawn from said high voltage power source (HV) through a load (31) comprising at least one of the transducer elements (16i) such that the amplitude of said low voltage power source (V PC ) controls the amplitude of the current from said high voltage source through said load (Fig. 3). An ultrasound imaging system as claimed in Claim 1, characterized in that the converter means (36) comprise a current gain transistor (Q2A), the base of said current gain transistor receiving said control voltage and a cascade of current amplifying transistors (Q2B) being connected to the emitter and collector of said current gain transistor; the coupling means (Q3) comprising a FET sourced by said current amplifiers (Q2B), the drain of said transistor being connected to said load (T), whereby current is drawn from said high voltage source (HV) through said transistor and said load (Fig. 3).

Inventors: RUSSELL ROBERT HEATHCOTE, SCHLEICHER ISRAEL DAVID, RUSSELL, ROBERT HEATHCOTE, SCHLEICHER, ISRAEL DAVID
Applicants: PHILIPS ELECTRONICS NA, PHILIPS ELECTRONICS NORTH AMERICA CORPORATION
Application year: 1988
Main classification: H03K17
IPC codes: G01N29, H03K17, A61B8, H04R3