CN112438756B - Ophthalmic ultrasonic imaging method, ophthalmic biomass measurement gain adjustment method and device - Google Patents

Abstract

The present invention provides an ophthalmic ultrasonic imaging method, a biomass measurement gain adjustment method and device, comprising: transmitting ultrasonic waves to an eyeball; receiving ultrasonic echoes reflected from the eyeball to obtain ultrasonic echo signals; obtaining measurement signals for reflecting multiple biomasses of the eyeball according to the ultrasonic echo signals; detecting multiple peaks from the measurement signal according to the ultrasonic reflection characteristics corresponding to each biomass, and obtaining the signal amplitude of each peak; if the signal amplitude of one or more peaks meets the preset conditions for gain adjustment, performing segmented gain adjustment on the measurement signal; and displaying the adjusted measurement signal. The present invention can automatically adjust the gain to a reasonable range according to the data status, thereby improving the accuracy of the measurement result and reducing the doctor's inspection operation.

Description

Ophthalmic ultrasonic imaging method, ophthalmic biomass measurement gain adjustment method and device

Technical Field

The present invention generally relates to the technical field of ophthalmic biomass measurement, and more specifically to an ophthalmic ultrasonic imaging method, a method for automatically adjusting an ophthalmic biomass measurement gain, an ophthalmic ultrasonic imaging device, and an ophthalmic biomass measurement device.

Background Art

A-ultrasound is also called A-type ultrasound. It detects the echo of sound waves based on the relationship between the time and amplitude of sound waves. Ophthalmic ultrasound imaging uses A-ultrasound to measure ophthalmic biomass. The principle is that when the probe is placed in front of the eyeball, the sound wave propagates forward. According to the propagation characteristics of the sound wave, each time it encounters an interface with density difference, a reflection occurs, forming a wave crest. In this way, the reflected echo will be arranged in sequence according to the return time. The height of the wave crest indicates the intensity of the echo. The higher the wave crest, the stronger the echo. A-ultrasound detects the position of the wave crest and calculates the corresponding eye biomass (such as the corneal thickness, anterior chamber depth, lens thickness, vitreous length and axial length of the eyeball) through sound velocity matching. However, since the sound wave propagates in tissues of different densities, the intensity of the echo will be different, so it is easy for some echoes to have very high peaks or even saturation; some echoes have very small peaks and no valid data can be detected.

Summary of the invention

In one aspect, the present invention provides an ophthalmic ultrasonic imaging method, the method comprising:

Sending ultrasound waves to the eyeball;

receiving an ultrasonic echo reflected from the eyeball to obtain an ultrasonic echo signal;

Obtaining measurement signals reflecting multiple biomass quantities of the eyeball according to the ultrasonic echo signal;

According to the ultrasonic reflection characteristics corresponding to each biomass, a plurality of peaks are detected from the measurement signal, and the signal amplitude of each peak is obtained;

If the signal amplitude of one or more of the peaks meets the preset condition of gain adjustment, performing segmented gain adjustment on the measurement signal; and

The adjusted measurement signal is displayed.

Another aspect of the present invention provides a method for automatically adjusting an ophthalmic biomass measurement gain, the method comprising:

Acquiring measurement signals for reflecting multiple biometrics of the eyeball;

According to the ultrasonic reflection characteristics corresponding to each biomass, a plurality of peaks are detected from the measurement signal, and the signal amplitude of each peak is obtained; and

When the signal amplitude of one or more of the peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal.

Exemplarily, when the signal amplitude of one or more of the peaks meets the gain adjustment condition, performing segmented gain adjustment on the measurement signal includes:

When the difference between the signal amplitudes of the peaks exceeds the set threshold, the signal amplitude of the peak with a smaller signal amplitude among the peaks is increased so that the difference between the signal amplitudes of the peaks does not exceed the set threshold.

Exemplarily, when the signal amplitude of one or more of the peaks meets the gain adjustment condition, performing segmented gain adjustment on the measurement signal includes:

When the signal amplitude of one or more of the peaks is lower than the peak of the set amplitude, the signal amplitude of the peak lower than the set amplitude is increased to at least not lower than the set amplitude.

Another aspect of the present invention provides an ophthalmic ultrasonic imaging device, comprising:

An ultrasonic probe, used for transmitting ultrasonic waves to the eyeball, and receiving ultrasonic echoes reflected from the eyeball to obtain ultrasonic echo signals;

Processor for:

Obtaining measurement signals reflecting multiple biomass quantities of the eyeball according to the ultrasonic echo signal;

According to the ultrasonic reflection characteristics corresponding to each biomass, a plurality of peaks are detected from the measurement signal, and the signal amplitude of each peak is obtained; and

When it is determined that the signal amplitude of one or more of the peaks meets the preset condition for gain adjustment, performing segmented gain adjustment on the measurement signal; and

A display is used to display the adjusted measurement signal.

Another aspect of the present invention provides an ophthalmic biomass measuring device, comprising:

one or more processors, working jointly or individually;

A memory storing one or more computer programs which, when executed by the one or more processors, cause the one or more processors to perform:

Acquiring measurement signals for reflecting multiple biometrics of the eyeball;

According to the ultrasonic reflection characteristics corresponding to each biomass, a plurality of peaks are detected from the measurement signal, and the signal amplitude of each peak is obtained; and

When it is determined that the signal amplitude of one or more of the peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal.

According to the ophthalmic ultrasonic imaging method, the method for automatically adjusting the gain of ophthalmic biomass measurement, the ophthalmic ultrasonic imaging device, and the ophthalmic biomass measurement device of the embodiments of the present invention, when it is determined that the signal amplitude of one or more peaks meets the gain adjustment conditions, the measurement signal is subjected to segmented gain adjustment, and the signal amplitude of each peak is adjusted to a reasonable range through the segmented gain adjustment, thereby improving the availability and accuracy of the measurement results and reducing the operation of the doctor's examination.

BRIEF DESCRIPTION OF THE DRAWINGS

In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings required for use in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings in the following description are only some embodiments of the present invention. For ordinary technicians in this field, other accompanying drawings can be obtained based on these accompanying drawings without paying creative labor.

FIG1 is a schematic diagram showing the structure of an exemplary ophthalmic ultrasonic imaging device for implementing the ophthalmic ultrasonic imaging method and device of the present invention;

FIG2 shows a schematic flow chart of an ophthalmic ultrasonic imaging method according to an embodiment of the present invention;

3A and 3B are schematic diagrams showing segmented gain adjustment in ophthalmic ultrasound imaging according to an embodiment of the present invention;

FIG4 shows a schematic structural block diagram of a processor of an ophthalmic ultrasonic imaging device according to an embodiment of the present invention;

FIG5 shows a schematic flow chart of a method for automatically adjusting an ophthalmic biomass measurement gain according to an embodiment of the present invention;

FIG. 6 shows a schematic structural block diagram of an ophthalmic biomass measurement device according to an embodiment of the present invention.

DETAILED DESCRIPTION

In order to make the purpose, technical scheme and advantages of the present invention more obvious, the exemplary embodiments according to the present invention will be described in detail with reference to the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments of the present invention, and it should be understood that the present invention is not limited to the exemplary embodiments described herein. Based on the embodiments of the present invention described in the present invention, all other embodiments obtained by those skilled in the art without creative work should fall within the protection scope of the present invention.

In the following description, a large number of specific details are provided to provide a more thorough understanding of the present invention. However, it is apparent to those skilled in the art that the present invention can be implemented without one or more of these details. In other examples, in order to avoid confusion with the present invention, some technical features well known in the art are not described.

It should be understood that the present invention can be implemented in different forms and should not be interpreted as limited to the embodiments set forth herein. On the contrary, these embodiments are provided to make the disclosure thorough and complete and to fully convey the scope of the present invention to those skilled in the art.

The purpose of the terms used herein is only to describe specific embodiments and is not intended to be limiting of the present invention. When used herein, the singular forms "one", "an" and "said/the" are also intended to include plural forms, unless the context clearly indicates otherwise. It should also be understood that the terms "consisting of" and/or "comprising", when used in this specification, determine the presence of the features, integers, steps, operations, elements and/or parts, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, parts and/or groups. When used herein, the term "and/or" includes any and all combinations of the relevant listed items.

In order to fully understand the present invention, a detailed structure will be proposed in the following description to illustrate the technical solution proposed by the present invention. The optional embodiments of the present invention are described in detail as follows, but in addition to these detailed descriptions, the present invention may also have other implementations.

Please refer to Figure 1, which shows a structural schematic diagram of an example ophthalmic ultrasonic imaging device 100 for implementing the ophthalmic ultrasonic imaging method and device of the present invention. The ultrasonic imaging device 100 includes an ultrasonic probe 101, a transmitting circuit 102, a receiving circuit 103, a processor 105 and a human-computer interaction device 106. The transmitting circuit 102 and the receiving circuit 103 can be connected to the ultrasonic probe 101 via a transmit/receive selection switch 107.

During ophthalmic ultrasound imaging, the transmitting circuit 102 sends a delayed focused transmitting pulse with a certain amplitude and polarity to the ultrasound probe 101 through the transmitting/receiving selection switch 107 to stimulate the ultrasound probe 101 to transmit ultrasound (e.g., transmit A-type ultrasound) to the eyeball. After a certain delay, the receiving circuit 103 receives the echo of the ultrasound through the transmitting/receiving selection switch 107 to obtain an ultrasound echo signal, and amplifies and performs analog-to-digital conversion on the echo signal, and then sends the processed ultrasound echo signal to the processor 105 for peak detection and other related processing to obtain the required A-ultrasound measurement signal. Through the position of each peak on the measurement signal, the corresponding eyeball biomass, such as the corneal thickness, anterior chamber depth, lens thickness, vitreous length and axial length of the eyeball, can be further calculated by methods such as sound velocity matching.

The human-machine interaction device 106 is connected to the processor 105. For example, the processor 105 can be connected to the human-machine interaction device 106 through an external input/output port. The human-machine interaction device 106 can detect the user's input information. The input information can be, for example, a control instruction for the ultrasonic emission and reception timing, an operation input instruction for editing and marking the measurement results of ophthalmic biomass, or other instruction types. The human-machine interaction device 106 can include a keyboard, a mouse, a scroll wheel, a trackball, a mobile input device (such as a mobile device with a touch screen, a mobile phone, etc.), a multi-function knob, etc., or a combination of multiple thereof. Therefore, the corresponding external input/output port can be a wireless communication module, or a wired communication module, or a combination of the two. The external input/output port can also be implemented based on USB, bus protocols such as CAN, and/or wired network protocols.

The human-computer interaction device 106 also includes a display, which can display the measurement signal obtained by the processor 105. In addition, while displaying the measurement signal, the display can also provide the user with a graphical interface for human-computer interaction, set one or more controlled objects on the graphical interface, and provide the user with the human-computer interaction device 106 to input operation instructions to control these controlled objects, thereby performing corresponding control operations. For example, an icon is displayed on the graphical interface, and the icon can be operated using the human-computer interaction device to perform a specific function, such as the function of marking the measurement results of ophthalmic biomass. In practical applications, the display can be a touch screen display. In addition, the display in this embodiment can include one display or multiple displays.

In the embodiment of the present invention, the processor 105 is used to process the ultrasonic echo signal to obtain a measurement signal for reflecting multiple biomasses of the eyeball; the processor 105 is also used to detect multiple peaks from the measurement signal according to the ultrasonic reflection characteristics corresponding to each biomass, and obtain the signal amplitude and position of each peak, and then calculate the corresponding eyeball biomass through sound velocity matching, the biomass includes, for example, corneal thickness, anterior chamber depth, lens thickness, vitreous length and axial length of the eyeball, wherein axial length = corneal thickness + anterior chamber depth + lens thickness + vitreous length. The human-computer interaction device 106 displays the detection result through a display, and the detection result includes parameter information and image information calculated by the processor 105.

FIG2 shows a schematic flow chart of an ophthalmic ultrasonic imaging method according to an embodiment of the present invention. As shown in FIG2 , the ophthalmic ultrasonic imaging method provided by this embodiment includes:

Step S201, transmitting ultrasound to the eyeball, for example, by controlling the ultrasound probe in the ophthalmic ultrasound imaging device shown in FIG1 to transmit ultrasound to the eyeball, illustratively, the ultrasound is A-type ultrasound.

Step S202, receiving the ultrasonic echo reflected from the eyeball to obtain an ultrasonic echo signal.

For example, by switching the ultrasonic probe to the receiving mode, the ultrasonic echo reflected by the eyeball is received, that is, the reflected sound wave signal is converted into an electrical signal through the receiving circuit.

Step S203: obtaining measurement signals for reflecting multiple biomasses of the eyeball according to the ultrasonic echo signal.

That is, by processing the ultrasonic echo signal, a measurement signal reflecting a plurality of biomass quantities of the eyeball is obtained.

Exemplarily, the plurality of biomasses are selected from the group consisting of: corneal thickness, anterior chamber depth, lens thickness, vitreous body length and axial length.

Exemplarily, in this embodiment, obtaining measurement signals for reflecting multiple biomass quantities of the eyeball according to the ultrasonic echo signal specifically includes the following steps:

A1, analog amplify the ultrasonic echo signal. That is, amplify the received ultrasonic echo signal to facilitate subsequent processing. The gain of the analog amplification can be performed according to the default setting or according to the pre-set setting.

A2, performing analog-to-digital conversion on the analog amplified ultrasonic echo signal, that is, converting the analog amplified ultrasonic echo signal into a digital signal. Exemplarily, it is advantageous to implement it through a corresponding analog-to-digital conversion circuit or chip.

A3, obtaining a measurement signal according to the ultrasound echo signal after analog-to-digital conversion. That is, the ultrasound echo signal after analog-to-digital conversion is processed to obtain a measurement signal reflecting multiple biomass of the eyeball, and the measurement signal can be represented as an image or a graph and displayed on a display. For example, the digital signal after analog-to-digital conversion can be adjusted for overall gain, and the adjusted signal can be subjected to signal envelope processing to form a measurement signal including multiple peaks. In some examples, pre-processing operations such as filtering can be further performed before the overall gain adjustment to improve the signal-to-noise ratio of the signal.

Since the analog-to-digital conversion of the receiving circuit/chip or processing circuit/chip of a general ultrasonic echo signal has a corresponding threshold (the analog signal exceeding the threshold will be clipped and cannot effectively reflect its size in the digital signal), when receiving or processing the ultrasonic echo signal, it is necessary to determine whether the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion (that is, whether the amplitude of some signals exceeds the conversion threshold of the analog-to-digital conversion), and when it is determined that the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion, adjust the analog gain of the analog amplification of the ultrasonic echo signal.

Exemplarily, in this embodiment, the corresponding circuit or chip in the ophthalmic ultrasonic imaging device can be used to determine whether the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion. For example, a comparison circuit can be used to determine whether the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion.

Exemplarily, in this embodiment, it also includes judging whether the signal strength after amplification exceeds the conversion threshold of analog-to-digital conversion through the waveform or graph of the ultrasonic echo signal. For example, if the waveform or graph of the ultrasonic echo signal is at the threshold value for a long time (the time can be determined based on experience or calculation), it means that this segment of the signal is a signal formed by clipping during the analog-to-digital conversion process, that is, the signal strength of the amplified ultrasonic echo signal exceeds the conversion threshold of analog-to-digital conversion.

When it is determined that the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion, the analog gain of the ultrasonic echo signal is adjusted. That is, in the process of analog amplification of the ultrasonic echo signal, the gain is adjusted. Exemplarily, the adjustment of the analog gain can be achieved by adjusting the gain value of part or all of the analog gain curve.

For the adjustment of analog gain, the appropriate analog gain can be directly calculated according to the conversion threshold and the signal strength amplitude of the analog amplified ultrasonic echo signal, and the calculated analog gain can be applied to the analog amplification link. For the adjustment of analog gain, a gain adjustment scheme can also be preset in the ophthalmic ultrasonic imaging device, for example, a certain gain value is lowered each time, and then it is judged whether the signal strength of the ultrasonic echo signal amplified by the gain value exceeds the conversion threshold. If it exceeds, the adjustment and judgment process is repeated until the signal strength of the analog amplified ultrasonic echo signal does not exceed the conversion threshold.

Step S204: Detect multiple peaks from the measurement signal according to the ultrasonic reflection characteristics corresponding to each biomass, and obtain the signal amplitude of each peak.

Exemplarily, according to the reflection duration of the ultrasonic wave corresponding to each biomass, multiple time ranges for peak detection in the measurement signal are determined, and peak signal detection is performed in each time range to determine multiple peaks. For example, corneal thickness and anterior chamber depth correspond to the first time range and the second time range, respectively, and peak detection is performed in the corresponding time range of the measurement signal. When a peak is detected in the first time range, it is considered that the peak is the peak corresponding to the corneal thickness. Similarly, the peak detected in the second time range is the peak corresponding to the anterior chamber depth. The processor further calculates the biomass of corneal thickness based on the position of the peak corresponding to the corneal thickness in combination with the sound velocity matching; similarly, the biomass of anterior chamber depth can be calculated. Peak detection based on the ultrasonic wave reflection characteristics corresponding to each biomass can improve the efficiency and accuracy of detection, and can be combined with the characteristics of each biomass. After the peak is detected, the biomass corresponding to the peak can be further calculated. The detection of the peak signal can be obtained by corresponding detection circuits and graphic processing. After multiple peaks are detected, the signal amplitude and position of each peak can be obtained.

Step S205: If the signal amplitude of one or more peaks meets the preset condition of gain adjustment, segmented gain adjustment is performed on the measurement signal.

Exemplarily, the preset condition is whether the difference between the signal amplitudes of each peak exceeds a set threshold value. If it is determined that the difference between the signal amplitudes of each peak exceeds the set threshold value, the measurement signal is subjected to segmented gain adjustment. For example, when the difference between the signal amplitudes of any two peaks exceeds the set threshold value, the measurement signal is subjected to segmented gain adjustment. Exemplarily, the signal amplitude of the peaks with smaller signal amplitudes among the peaks can be increased so that the difference between the signal amplitudes of the peaks does not exceed the set threshold value. That is, the signal amplitudes of the peaks are close to each other, so that the user can obtain more accurate measurement results based on the adjusted peaks.

Exemplarily, the preset condition is whether the signal amplitude of each peak is lower than the set amplitude. If it is determined that there is a peak with a signal amplitude lower than the set amplitude in the measurement signal, the peak with a signal amplitude lower than the set amplitude in the measurement signal is adjusted in sections. Exemplarily, the measurement signal can be adjusted in sections by increasing the signal amplitude of the peak lower than the set amplitude to at least not lower than the set amplitude. That is, the signal of each peak is made to at least reach the set amplitude, and the set amplitude can meet the needs of further calculating the biomass to a certain extent.

Exemplarily, the preset conditions may include whether the difference between the signal amplitudes of the various peaks exceeds a set threshold and whether the signal amplitude of each peak is lower than a set amplitude. That is, it includes both the determination of the difference in signal amplitudes between the peaks and the determination of whether the signal amplitude of the peaks is lower than a set amplitude. Through the two-way signal analysis and segmented gain adjustment, the adjusted measurement signal can not only have multiple similar peaks, but also the signals of each peak meet the requirements for further calculation of biomass.

In this embodiment, the segmented gain adjustment of the measurement signal can be achieved by superimposing a segmented gain adjustment curve on the curve of the original measurement signal. Figures 3A and 3B show a schematic schematic diagram of segmented gain adjustment in ophthalmic ultrasonic imaging according to an embodiment of the present invention. As shown in Figures 3A and 3B, curve 1 in Figure 3A represents a curve without segmented gain adjustment, and the difference between the amplitude of the first two peaks and the amplitude of the latter peak exceeds the set threshold, or the amplitude of the first two peaks is lower than the set amplitude, which is not conducive to accurately obtaining the peak position, thereby affecting the accuracy of the measurement result. Therefore, segmented gain adjustment is required, and the curve in Figure 3A is a 2-segmented gain adjustment curve. The graph of curve 1 and curve 2 in Figure 3A after superposition (i.e., segmented gain adjustment) is shown in Figure 3B. It can be seen from Figure 3B that after segmented gain adjustment, the peak with a smaller amplitude originally increases, which is more conducive to doctor observation and acquisition of peak position.

Step S206, displaying the adjusted measurement signal.

That is, the gain-adjusted measurement signal is displayed on the display, so that the position of each peak can be obtained according to the measurement signal, and the detection result, that is, the eyeball biomass, can be obtained accordingly.

In addition, it should be understood that in the ophthalmic ultrasonic imaging method of the present embodiment, it may be necessary to perform analog gain adjustment of the ultrasonic echo signal and segmented gain adjustment of the measurement signal, and the gain adjustment will affect the acquisition of subsequent detection results. Therefore, after the analog gain adjustment of the ultrasonic echo signal and/or the segmented gain adjustment of the measurement signal, the measurement signal needs to be processed again to regain multiple peaks and the signal amplitude and position of each peak based on the adjusted measurement signal, and then calculate the corresponding eyeball biomass through sound velocity matching according to the position of each peak.

According to the ophthalmic ultrasonic imaging method of an embodiment of the present invention, when it is determined that the signal amplitude of one or more peaks meets the gain adjustment conditions, the measurement signal is subjected to segmented gain adjustment, and the signal amplitude of one or more peaks is adjusted to within a reasonable range through the segmented gain adjustment, thereby improving the accuracy of the measurement result. In addition, since the segmented gain adjustment is automatically completed, the number of operations required to obtain the measurement signal desired by the doctor can be reduced, the doctor's examination operations are reduced, and the doctor's examination efficiency is improved.

FIG. 4 shows a schematic structural block diagram of a processor of an ophthalmic ultrasonic imaging device according to an embodiment of the present invention.

As shown in FIG. 4 , the processor 105 includes an analog amplification module 431 , an analog-to-digital conversion module 432 , a signal processing module 433 , a determination module 434 , a gain adjustment module 435 and a detection result acquisition module 436 .

The analog amplification module 431 is used to perform analog amplification on the ultrasonic echo signal received by the ultrasonic probe to facilitate subsequent processing. The gain of the analog amplification can be performed according to the default setting or according to the pre-setting. The analog amplification module 431 can be implemented as various analog amplification circuits or chips, and the analog amplification circuit can be a single-stage amplification circuit or a multi-stage amplification circuit.

The analog-to-digital conversion module 432 is used to perform analog-to-digital conversion on the ultrasonic echo signal after analog amplification by the analog amplification module 431. The analog-to-digital conversion module 432 can be implemented as an analog-to-digital conversion circuit or chip.

The signal processing module 433 is used to obtain a measurement signal according to the ultrasonic echo signal after analog-to-digital conversion, and detect multiple peaks from the measurement signal according to the ultrasonic reflection characteristics corresponding to each biomass, and obtain the signal amplitude of each peak. Exemplarily, the signal processing module 433 determines multiple time ranges for peak detection in the measurement signal according to the reflection duration of the ultrasonic wave corresponding to each biomass, and performs peak signal detection in each time range to determine multiple peaks. The signal processing module 433 can be implemented as a processing circuit or a processor, and the processor implements the functions of the signal processing module 433 by executing a corresponding computer program.

The judgment module 434 is used to judge whether the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of analog-to-digital conversion, and whether the signal amplitude of one or more peaks meets the preset conditions of gain adjustment. The judgment module 434 can be implemented as a corresponding circuit or processor, and the processor implements the function of the judgment module 434 by executing a corresponding computer program.

If the judgment module 434 determines that the signal strength of the ultrasonic echo signal after analog amplification exceeds the conversion threshold of the analog-to-digital conversion, the gain adjustment module 435 adjusts the analog gain of the analog amplification of the ultrasonic echo signal. Exemplarily, the gain adjustment module 435 adjusts the gain value of part or all of the analog gain curve to prevent the ultrasonic echo signal after analog amplification from being too large and exceeding the conversion threshold of the analog-to-digital conversion.

If the determination module 434 determines that the signal amplitude of one or more peaks meets the preset condition for gain adjustment, the gain adjustment module 435 performs segmented gain adjustment on the measurement signal.

Exemplarily, the preset condition is whether the difference between the signal amplitudes of each peak exceeds a set threshold value. If the judgment module 434 determines that the difference between the signal amplitudes of each peak exceeds the set threshold value, the gain adjustment module 435 performs segmented gain adjustment on the measurement signal. Exemplarily, the gain adjustment module 435 can perform segmented gain adjustment on the measurement signal by increasing the signal amplitude of the peak with a smaller signal amplitude among each peak so that the difference between the signal amplitudes of each peak does not exceed the set threshold value.

Exemplarily, the preset condition is whether the signal amplitude of each peak is lower than the set amplitude. If the judgment module 434 determines that there is a peak with a signal amplitude lower than the set amplitude in the measurement signal, the gain adjustment module 435 performs segmented gain adjustment on the peaks in the measurement signal that are lower than the set amplitude. Exemplarily, the gain adjustment module 435 can perform segmented gain adjustment on the measurement signal by increasing the signal amplitude of the peaks that are lower than the set amplitude to at least not lower than the set amplitude.

The process or principle of segmented gain adjustment is shown in FIG. 3A and FIG. 3B , and will not be described in detail here.

The detection result acquisition module 436 is used to calculate the corresponding eyeball biomass through sound velocity matching according to the positions of multiple wave peaks detected in the measurement signal.

Exemplarily, the determination module 434, the gain adjustment module 435 and the detection result acquisition module 436 may be implemented by a processor executing corresponding computer programs.

It should be understood that after the processor performs analog gain adjustment on the ultrasonic echo signal and/or segmented gain adjustment on the measurement signal, it is necessary to process the measurement signal again to regain multiple peaks and the signal amplitude and position of each peak based on the adjusted measurement signal, and then calculate the corresponding eye biomass through sound speed matching based on the position of each peak.

The display is used to display the adjusted measurement signal and detection result.

According to the ophthalmic ultrasonic imaging device of an embodiment of the present invention, when it is determined that the signal amplitude of one or more peaks meets the gain adjustment conditions, the measurement signal is subjected to segmented gain adjustment. The signal amplitude of each peak is adjusted to within a reasonable range through the segmented gain adjustment, thereby improving the accuracy of the measurement result. In addition, since the segmented gain adjustment is automatically completed, the number of operations required to obtain the measurement signal desired by the doctor can be reduced, the doctor's examination operations are reduced, and the doctor's examination efficiency is improved.

FIG. 5 shows a schematic flow chart of a method for automatically adjusting an ophthalmic biomass measurement gain according to an embodiment of the present invention.

As shown in FIG5 , the method for automatically adjusting the ophthalmic biomass measurement gain provided in this embodiment includes:

Step S601, obtaining measurement signals for reflecting multiple biomass of the eyeball. The measurement signals can be obtained by transmitting ultrasound to the eyeball, receiving ultrasound echo signals, and then processing the ultrasound echo signals. The measurement signals can also be obtained from the internal memory of the ophthalmic ultrasound imaging device or from an external device. Biomass, for example, includes corneal thickness, anterior chamber depth, lens thickness, vitreous length, and axial length of the eyeball.

Step S602: Detect multiple peaks from the measurement signal according to the ultrasonic reflection characteristics corresponding to each biomass, and obtain the signal amplitude of each peak.

Exemplarily, according to the reflection duration of the ultrasonic wave corresponding to each biomass, multiple time ranges for performing peak detection in the measurement signal are determined, and peak signal detection is performed in each time range to determine multiple peaks.

Step S603: When the signal amplitude of one or more peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal.

Exemplarily, the gain adjustment condition is whether the difference between the signal amplitudes of each peak exceeds a set threshold value. If it is determined that the difference between the signal amplitudes of two or more peaks in each peak exceeds the set threshold value, the measurement signal is subjected to segmented gain adjustment. Exemplarily, the measurement signal can be subjected to segmented gain adjustment by increasing the signal amplitude of the peak with a smaller signal amplitude in each peak so that the difference between the signal amplitudes of each peak does not exceed the set threshold value.

Exemplarily, the gain adjustment condition is whether the signal amplitude of each peak is lower than the set amplitude. If it is determined that there is a peak with a signal amplitude lower than the set amplitude in the measurement signal, the peak with the signal amplitude lower than the set amplitude in the measurement signal is subjected to segmented gain adjustment. Exemplarily, the segmented gain adjustment of the measurement signal can be performed by increasing the signal amplitude of the peak lower than the set amplitude to at least not lower than the set amplitude.

In this embodiment, the segmented gain adjustment of the measurement signal can be achieved by superimposing a segmented gain adjustment curve on the curve of the original measurement signal. Figures 3A and 3B show schematic principle diagrams of segmented gain adjustment in ophthalmic ultrasound imaging according to an embodiment of the present invention.

FIG. 6 shows a schematic structural block diagram of an ophthalmic biomass measurement device according to an embodiment of the present invention.

As shown in FIG6 , the ophthalmic biomass measuring device 700 provided in this embodiment includes one or more processors 710, working together or individually; one or more memories 720, wherein the one or more memories 720 store one or more computer programs, and when the one or more computer programs are executed by the one or more processors, the one or more processors 710 execute:

Acquiring measurement signals for reflecting multiple biometrics of the eyeball;

According to the ultrasonic reflection characteristics corresponding to each biomass, a plurality of peaks are detected from the measurement signal, and the signal amplitude of each peak is obtained; and

When it is determined that the signal amplitude of one or more peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal.

When the signal amplitude of one or more of the peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal, including:

When the difference between the signal amplitudes of the peaks exceeds the set threshold, the signal amplitude of the peak with the smaller signal amplitude among the peaks is increased so that the difference between the signal amplitudes of the peaks does not exceed the set threshold.

When the signal amplitude of one or more peaks meets the gain adjustment condition, segmented gain adjustment is performed on the measurement signal, including:

When the signal amplitude of one or more peaks is lower than the peak of the set amplitude, the signal amplitude of the peak lower than the set amplitude is increased to at least not lower than the set amplitude.

In addition, an embodiment of the present invention further provides a computer storage medium on which a computer program is stored. One or more computer program instructions may be stored on the computer-readable storage medium, and the processor may run the program instructions stored in the storage device to implement the functions (implemented by the processor) in the embodiments of the present invention described herein and/or other desired functions, such as to execute the corresponding steps of the ophthalmic ultrasonic imaging method and the method for automatically adjusting the gain of ophthalmic biomass measurement according to the embodiments of the present invention. Various applications and various data, such as various data used and/or generated by the application, may also be stored in the computer-readable storage medium.

For example, the computer storage medium may include a memory card, a storage component of a tablet computer, a hard disk of a personal computer, a read-only memory (ROM), an erasable programmable read-only memory (EPROM), a portable compact disk read-only memory (CD-ROM), a USB memory, or any combination of the above storage media.

In summary, according to the ophthalmic ultrasonic imaging method, the method for automatically adjusting the ophthalmic biomass measurement gain, the ophthalmic ultrasonic imaging device, and the ophthalmic biomass measurement device of the embodiments of the present invention, when it is determined that the signal amplitude of one or more peaks meets the gain adjustment conditions, the measurement signal is subjected to segmented gain adjustment, and the signal amplitude of each peak is adjusted to within a reasonable range through the segmented gain adjustment, thereby improving the accuracy of the measurement result and reducing the operation of the doctor's examination.

The segmented gain adjustment described in the present invention means that when the gain adjustment is performed on the measurement signal, it is not required to perform an overall and unified gain adjustment on the measurement signal, but to adjust the signal segment of the measurement signal that needs to be adjusted, and the degree and method of adjusting the signal segment that needs to be adjusted can be different. For example, the segmented gain adjustment can be to perform a gain adjustment on one or several peaks of multiple peaks, or to perform a gain adjustment on all peaks of multiple peaks. For example, the segmented gain adjustment can be to amplify the signal amplitude of one peak to twice the amplitude before adjustment, and to amplify the signal amplitude of another peak to three times the amplitude before adjustment. In addition, the segmented gain adjustment of the measurement signal is for the peak-containing signal obtained after envelope processing. The purpose of the gain adjustment is to amplify the signal amplitude of the peak within the envelope range, and it is not expected to synchronously amplify the signal outside the envelope. Therefore, the gain-adjusted signal or curve corresponds to the envelope of the measurement signal, especially to the peak, forming a segmented gain adjustment signal or curve with a sudden change in gain value.

Although example embodiments have been described herein with reference to the accompanying drawings, it should be understood that the above example embodiments are merely exemplary and are not intended to limit the scope of the present invention thereto. Various changes and modifications may be made therein by one of ordinary skill in the art without departing from the scope and spirit of the present invention. All such changes and modifications are intended to be included within the scope of the present invention as required by the appended claims.

Those skilled in the art will appreciate that the units and algorithm steps of each example described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of the present invention.

In the several embodiments provided in this application, it should be understood that the disclosed devices and methods can be implemented in other ways. For example, the device embodiments described above are only schematic, for example, the division of the units is only a logical function division, and there may be other division methods in actual implementation, such as multiple units or components can be combined or integrated into another device, or some features can be ignored or not executed.

In the description provided herein, a large number of specific details are described. However, it is understood that embodiments of the present invention can be practiced without these specific details. In some instances, well-known methods, structures and techniques are not shown in detail so as not to obscure the understanding of this description.

Similarly, it should be understood that in order to streamline the present invention and help understand one or more of the various inventive aspects, in the description of the exemplary embodiments of the present invention, the various features of the present invention are sometimes grouped together into a single embodiment, figure, or description thereof. However, the method of the present invention should not be interpreted as reflecting the following intention: the claimed invention requires more features than the features explicitly stated in each claim. More specifically, as reflected in the corresponding claims, the inventive point is that the corresponding technical problem can be solved with less than all the features of a single disclosed embodiment. Therefore, the claims following the specific embodiment are hereby expressly incorporated into the specific embodiment, wherein each claim itself serves as a separate embodiment of the present invention.

It will be understood by those skilled in the art that, except for mutually exclusive features, all features disclosed in this specification (including the accompanying claims, abstracts and drawings) and all processes or units of any method or device disclosed in this specification may be combined in any combination. Unless otherwise expressly stated, each feature disclosed in this specification (including the accompanying claims, abstracts and drawings) may be replaced by an alternative feature that provides the same, equivalent or similar purpose.

In addition, those skilled in the art will appreciate that, although some embodiments described herein include certain features included in other embodiments but not other features, the combination of features of different embodiments is meant to be within the scope of the present invention and form different embodiments. For example, in the claims, any one of the claimed embodiments may be used in any combination.

The various component embodiments of the present invention can be implemented in hardware, or in software modules running on one or more processors, or in a combination thereof. It should be understood by those skilled in the art that a microprocessor or digital signal processor (DSP) can be used in practice to implement some or all of the functions of some modules according to embodiments of the present invention. The present invention can also be implemented as a device program (e.g., a computer program and a computer program product) for executing part or all of the methods described herein. Such a program implementing the present invention can be stored on a computer-readable medium, or can have the form of one or more signals. Such a signal can be downloaded from an Internet website, or provided on a carrier signal, or provided in any other form.

It should be noted that the above embodiments illustrate rather than limit the invention, and that those skilled in the art may devise alternative embodiments without departing from the scope of the appended claims. In the claims, any reference symbol between brackets shall not be construed as a limitation on the claims. The invention may be implemented by means of hardware comprising a number of different elements and by means of a suitably programmed computer. In a unit claim enumerating a number of means, several of these means may be embodied by the same hardware item. The use of the words first, second, and third, etc., does not indicate any order. These words may be interpreted as names.

Claims (11)

1. An ophthalmic ultrasound imaging method, comprising:

Transmitting ultrasonic waves to the eyeball;

receiving an ultrasonic echo reflected by the eyeball to obtain an ultrasonic echo signal;

Obtaining measurement signals reflecting a plurality of biomass of the eyeball according to the ultrasonic echo signals;

detecting a plurality of wave peaks from the measurement signals according to the ultrasonic reflection characteristics corresponding to the biomass, and obtaining the signal amplitude of each wave peak;

If the signal amplitude of one or more wave peaks accords with the preset condition of gain adjustment, carrying out segment gain adjustment on the measurement signal, wherein the segment gain adjustment comprises the following steps: determining whether the signal amplitudes of the wave crests differ by more than a set threshold value, and increasing the signal amplitudes of the wave crests with smaller signal amplitudes in the wave crests when the situation that the signal amplitudes differ by more than the set threshold value exists in the wave crests so that the difference value between the signal amplitudes of the wave crests does not exceed the set threshold value; and

Displaying the adjusted measurement signal.

2. The method of claim 1, wherein after the segment gain adjustment is performed on the measurement signal, the measurement signal is processed again to recover the plurality of peaks and the signal amplitudes of the respective peaks based on the adjusted measurement signal.

3. The method of claim 1, wherein detecting a plurality of peaks from the measurement signal based on the ultrasound reflection characteristics for each biomass, comprises:

and determining a plurality of time ranges for detecting the wave peaks in the measurement signals according to the reflection time periods of the ultrasonic waves corresponding to the biomass, and detecting peak signals in the time ranges to determine a plurality of wave peaks.

4. A method according to any one of claims 1-3, wherein the plurality of biomass is selected from the group consisting of: the cornea thickness, anterior chamber depth, lens thickness, vitreous length, and ocular axis length.

5. The method of claim 1, wherein deriving measurement signals reflecting a plurality of biomass of the eyeball from the ultrasonic echo signals comprises:

Analog amplification of the ultrasonic echo signal is performed,

Analog-to-digital conversion is carried out on the analog amplified ultrasonic echo signals; and

Obtaining the measurement signal according to the analog-to-digital converted ultrasonic echo signal;

The method further comprises the steps of: and when the signal intensity of the ultrasonic echo signal after analog amplification exceeds the conversion threshold value of analog-to-digital conversion, adjusting the analog gain for analog amplification of the ultrasonic echo signal.

6. The method of claim 5, wherein adjusting the analog gain comprises adjusting a gain value of a portion or an entirety of an analog gain curve.

7. A method for automatically adjusting ophthalmic biomass measurement gain, comprising:

Acquiring measurement signals reflecting a plurality of biomass of an eyeball;

detecting a plurality of wave peaks from the measurement signals according to the ultrasonic reflection characteristics corresponding to the biomass, and obtaining the signal amplitude of each wave peak; and

When the signal amplitude of one or more wave crests meets the gain adjustment condition, carrying out segment gain adjustment on the measurement signal, wherein the segment gain adjustment comprises the following steps: when the phase difference between the signal amplitudes of the wave peaks exceeds a set threshold, increasing the signal amplitude of the wave peak with smaller signal amplitude in the wave peaks so that the difference between the signal amplitudes of the wave peaks does not exceed the set threshold.

8. An ophthalmic ultrasound imaging device, comprising:

The ultrasonic probe is used for transmitting ultrasonic waves to the eyeball and receiving ultrasonic echoes reflected by the eyeball to obtain ultrasonic echo signals;

A processor for:

Obtaining measurement signals reflecting a plurality of biomass of the eyeball according to the ultrasonic echo signals;

detecting a plurality of wave peaks from the measurement signals according to the ultrasonic reflection characteristics corresponding to the biomass, and obtaining the signal amplitude of each wave peak; and

When determining that the signal amplitude of one or more wave crests meets the preset condition of gain adjustment, carrying out segment gain adjustment on the measurement signal, wherein the segment gain adjustment comprises the following steps: determining whether the signal amplitudes of the wave crests differ by more than a set threshold value, and increasing the signal amplitude of the wave crest with smaller signal amplitude in the wave crest when the situation that the signal amplitudes differ by more than the set threshold value exists in the wave crest, so that the difference value between the signal amplitudes of the wave crest does not exceed the set threshold value; and

And the display is used for displaying the adjusted measurement signal.

9. The ophthalmic ultrasound imaging device of claim 8, wherein the processor detects a plurality of peaks from the measurement signal based on ultrasound reflection characteristics corresponding to each biomass, comprising:

and determining a plurality of time ranges for detecting the wave peaks in the measurement signals according to the reflection time periods of the ultrasonic waves corresponding to the biomass, and detecting peak signals in the time ranges to determine a plurality of wave peaks.

10. The ophthalmic ultrasound imaging device of any of claims 8-9, wherein the processor deriving measurement signals reflecting a plurality of biomass of the eyeball from the ultrasound echo signals comprises:

Analog amplification of the ultrasonic echo signal is performed,

Analog-to-digital conversion is carried out on the analog amplified ultrasonic echo signals; and

Obtaining the measurement signal according to the analog-to-digital converted ultrasonic echo signal;

The processor is further configured to adjust an analog gain for analog amplification of the ultrasound echo signal when it is determined that the signal strength of the analog amplified ultrasound echo signal exceeds a conversion threshold of analog-to-digital conversion.

11. An ophthalmic biomass measurement device, comprising:

one or more processors working together or individually;

A memory storing one or more computer programs that, when executed by the one or more processors, cause the one or more processors to perform:

Acquiring measurement signals reflecting a plurality of biomass of an eyeball;

detecting a plurality of wave peaks from the measurement signals according to the ultrasonic reflection characteristics corresponding to the biomass, and obtaining the signal amplitude of each wave peak; and

When it is determined that the signal amplitudes of one or more of the peaks meet a gain adjustment condition, performing a segmented gain adjustment on the measurement signal, including: determining whether the signal amplitudes of the wave crests differ by more than a set threshold value, and increasing the signal amplitudes of the wave crests with smaller signal amplitudes in the wave crests when the situation that the signal amplitudes differ by more than the set threshold value exists in the wave crests, so that the difference value between the signal amplitudes of the wave crests does not exceed the set threshold value.