Description:TECHNICAL FIELD
The present disclosure relates generally to the field of health monitoring devices and, more specifically, to an apparatus for measuring the concentration of chiral molecules.
BACKGROUND
In the field of health monitoring devices, chiral molecule sensing devices are used to measure concentration of chiral molecules in liquid samples or bodily fluids from human or animal bodies. In the context of a human body, analytical devices, such as glucometers, are used to draw venal blood from the human body and perform further laboratory analysis to determine the concentration of the chiral molecules. However, conventional chiral molecule sensing devices that are used for measuring the concentration of the chiral molecules are invasive in nature and may result in potential skin deformations, causing prolonged pain in the human body that could also lead to the risk of infection, scarring, and fatigue.
Currently, certain attempts have been made to avoid problems associated with the conventional invasive chiral molecule sensing devices by developing non-invasive chiral molecule sensing devices. Moreover, conventional non-invasive chiral molecule sensing devices operate on the principle of spectroscopy and on the principle of electrochemical reaction that includes an infrared spectroscopy, a Raman spectroscopy, and the like. However, the challenges associated with the conventional non-invasive chiral molecule sensing devices include measuring the glucose concentrations at deep tissue levels. In addition, the conventional non-invasive chiral molecule sensing devices are not effective in measuring the concentration of the chiral molecules after a few millimetres beyond the skin. Therefore, there exists a technical problem of how to measure the concentration of the chiral molecules at a deep level by preventing loss of linearity during measurement accurately and reliably as compared to the conventional non-invasive chiral molecule sensing devices.
Therefore, in light of the foregoing discussion, there exists a need to overcome the aforementioned drawbacks associated with the conventional non-invasive chiral molecule sensing devices.
SUMMARY
The present disclosure provides a non-invasive measurement apparatus for measuring the concentration of chiral molecules. The present disclosure provides a solution to the technical problem of how to measure the concentration of the chiral molecules at a deep level by preventing loss of linearity during measurement accurately and reliably as compared to conventional non-invasive chiral molecule sensing devices. An aim of the present disclosure is to provide a solution that overcomes at least partially the problems encountered in the prior art and provide an improved apparatus that measures the concentration of the chiral molecules based on optical and photoacoustic characteristics of a test sample accurately, non-invasively, and reliably.
One or more objectives of the present disclosure are achieved by the solutions provided in the enclosed independent claims. Advantageous implementations of the present disclosure are further defined in the dependent claims.
In one aspect, the present disclosure provides an apparatus for measuring the concentration of the chiral molecules. The apparatus includes a test sample holder to hold one or more test samples and is configured to receive a beam of light in a first state of polarization. The one or more test samples rotate the beam of light from the first state of polarization to a second state of polarization and concomitantly generate photoacoustic waves. Furthermore, the apparatus includes a transducer that is configured to receive the photoacoustic waves generated within the one or more test samples and convert the photoacoustic waves into photoacoustic electrical signals. The photoacoustic electrical signals are a time series dataset, which is a function of depth in the one or more test samples. The apparatus further includes a processor that is communicatively coupled to the transducer. Furthermore, the processor is configured to determine an angle of rotation between the first state of polarization and the second state of polarization based on the recorded photoacoustic electrical signals and determine the concentration of the chiral molecules in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization.
Advantageously, the apparatus is designed for the non-invasive measurement of the concentrations of the chiral molecules in one or more test samples efficiently, effectively, and accurately. The test sample holder receives a polarized beam of light that is rotated by the chiral molecules in the one or more test samples, generating further photoacoustic waves. The optical rotation of the beam of light, from the first state of polarization to the second state of polarization, provides precise depth-specific information, offering a comprehensive analysis of the chiral molecule concentration in the one or more test samples. The transducer converts the photoacoustic waves within the one or more test samples into time-series photoacoustic electrical signals, providing a depth-dependent dataset (i.e., a time-series dataset) to allow spatial-temporal analysis of the one or more test samples. Furthermore, by analyzing the pressure changes in the photoacoustic waves, the processor is configured to calculate the angle of rotation, allowing an accurate determination of the concentration of the chiral molecules. The apparatus is configured to analyze bodily fluids, body tissue, or optically active liquid solutions, thereby providing a non-invasive way of measuring the concentration of the chiral molecules. As a result, the apparatus provides a non-invasive and depth-specific measurement of the concentration of the chiral molecules with enhanced accuracy and reliability, offering a painless and convenient way to measure and monitor the level (or concentration) of the chiral molecules in the human body.
In an implementation form, the processor is configured to determine the change in pressure observed in the photoacoustic waves by deconvoluting the transducer response from the photoacoustic electrical signals generated by the transducer.
Advantageously, due to deconvoluting the transducer response from the photoacoustic electrical signals, the processor is configured to obtain the photoacoustic electrical signals that are further utilized to measure the concentration of the chiral molecules accurately.
In a further implementation form, the apparatus further includes the light source configured to emit the beam of light directly in the first state of polarization to reach to the one or more test samples.
In such an implementation, the utilization of specific polarization states, such as linear, vertical, and circular, provides a precise measurement of the chiral molecules within the one or more test samples.
In a further implementation form, the apparatus further comprises the light source and the one or more polarizing optics. The light source is configured to emit a beam of light in an unpolarized state towards the one or more polarizing optics. Moreover, the one or more polarizing optics are configured to convert the beam of light in the unpolarized state into a polarized state corresponding to the first state of polarization to reach to the one or more test samples.
Advantageously, the conversion of the beam of light from the unpolarized state to the polarized state enhances the flexibility, providing a convenient and efficient way to achieve the desired polarization conditions without relying on a specialized polarized light source. As a result, such conversion enhances the practicality and cost-effectiveness of the apparatus for measuring the concentration of the chiral molecules within the one or more test samples.
It is to be appreciated that all the aforementioned implementation forms can be combined. All steps which are performed by the various entities described in the present application as well as the functionalities described to be performed by the various entities are intended to mean that the respective entity is adapted to or configured to perform the respective steps and functionalities. It will be appreciated that features of the present disclosure are susceptible to being combined in various combinations without departing from the scope of the present disclosure as defined by the appended claims.
Additional aspects, advantages, features, and objects of the present disclosure would be made apparent from the drawings and the detailed description of the illustrative implementations construed in conjunction with the appended claims that follow.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a block diagram of an apparatus for measuring concentration of chiral molecules, in accordance with an embodiment of the present disclosure;
FIG. 2A is a diagram of the apparatus for measuring the concentration of the chiral molecules, in accordance with an embodiment of the present disclosure;
FIG. 2B is another diagram of another apparatus for measuring the concentration of the chiral molecules, in accordance with another embodiment of the present disclosure;
FIGs. 3A, 3B, 3C, and 3D are graphical representations depicting a calculation of photoacoustic rotation from a time-series photoacoustic electrical signals, in accordance with an embodiment of the present disclosure;
FIG. 4A is a graphical representation of a calculated rotation varying with concentration for a vertical incidence in an aqueous chiral molecular solution, in accordance with an embodiment of the present disclosure.
FIG. 4B is a graphical representation of a calculated rotation varying with concentration for a vertical incidence in a bovine serum albumin chiral molecular solution, in accordance with an embodiment of the present disclosure;
FIG. 5A is a graphical representation of Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a vertical incidence, in accordance with an embodiment of the present disclosure;
FIG. 5B is a graphical representation of the Clarke’s error grid analysis (CEGA) for the bovine serum albumin dissolved glucose solution for the vertical incidence, in accordance with an embodiment of the present disclosure;
FIG. 5C is a graphical representation of the Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a linear incidence, in accordance with an embodiment of the present disclosure;
FIG. 5D is a graphical representation of the Clarke’s error grid analysis (CEGA) for the bovine serum albumin glucose solution for the linear incidence, in accordance with an embodiment of the present disclosure;
FIG. 5E is a graphical representation of the Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a circular incidence, in accordance with an embodiment of the present disclosure; and
FIG. 5F is a graphical representation of the Clarke’s error grid analysis (CEGA) for the bovine serum albumin glucose solution for the circular incidence, in accordance with an embodiment of the present disclosure.
The summary above, as well as the following detailed description of illustrative embodiments, is better understood when read in conjunction with the appended drawings. For the purpose of illustrating the present disclosure, exemplary constructions of the disclosure are shown in the drawings. However, the present disclosure is not limited to specific methods and instrumentalities disclosed herein. Moreover, those skilled in the art will understand that the drawings are not to scale. Wherever possible, like elements have been indicated by identical numbers.
Embodiments of the present disclosure will now be described, by way of example only, with reference to the following diagrams wherein:
In the accompanying drawings, an underlined number is employed to represent an item over which the underlined number is positioned or an item to which the underlined number is adjacent. A non-underlined number relates to an item identified by a line linking the non-underlined number to the item. When a number is non-underlined and accompanied by an associated arrow, the non-underlined number is used to identify a general item at which the arrow is pointing.
DETAILED DESCRIPTION OF EMBODIMENTS
The following detailed description illustrates embodiments of the present disclosure and ways in which they can be implemented. Although some modes of carrying out the present disclosure have been disclosed, those skilled in the art would recognize that other embodiments for carrying out or practicing the present disclosure are also possible.
FIG. 1 is a schematic block diagram of an apparatus for measuring a concentration of chiral molecules, in accordance with an embodiment of the present disclosure. With reference to FIG. 1, there is shown a block diagram 100 that depicts an apparatus, 102 for measuring the concentration of the chiral molecules. The apparatus 102 includes a light source 104, a one or more polarizing optics 106, a test sample holder 108, a transducer 110, and a processor 112.
It may be understood by a person skilled in the art that the FIG. 1, which is the block diagram 100 of the apparatus 102, is considered as a simple one for the sake of brevity, which should not unduly limit the scope of the claims herein. The person skilled in the art will recognize many variations, alternatives, and modifications of embodiments of the present disclosure.
There is provided the apparatus 102 for measuring the concentration of the chiral molecules in one or more test samples placed within the test sample holder 108 based on the optical characteristics of the one or more test samples. Alternatively, the apparatus 102 is configured to monitor the concentration of the chiral molecules based on the optical characteristics of the one or more test samples. Moreover, the optical characteristics refer to the behaviour of the chiral molecules within one or more test samples due to interaction with the light that allows the change in the state of the light. Furthermore, the apparatus 102 operates non-invasively, which means that such measurement does not involve penetration or breaking of the skin, entry into a body cavity, or any other intrusion into a human body to collect the test samples. As a result, the apparatus 102 is used for non-invasive measurement of the concentration of the chiral molecules accurately, efficiently, and reliably. In addition, the apparatus 102 also prevents a patient (or the human body) from continuous invasion that may lead to an infection, scarring, or fatigue.
The apparatus 102 includes the test sample holder 108 to hold one or more test samples. In an implementation, the test sample holder 108 is positioned adjacent to (subsequent to) the one or more polarizing optics 106. The test sample holder 108 refers to a three-dimensional storage space, which is configured to hold one or more test samples. Examples of the test sample holder 108 may include, but are not limited to, test tubes, biopsy holders, microfluidic chips, beakers, cartridges, and the like that can store the one or more test samples. Furthermore, the test sample holder 108 is configured to receive the beam of light in the first state of polarization. In an implementation, the first state of polarization refers to the orientation of electromagnetic field vectors (or dipoles) within the beam of light. The one or more test samples rotate the beam of light from the first state of polarization to a second state of polarization and concomitantly generate photoacoustic waves. In an implementation, the second state of polarization refers to the orientation of electromagnetic field vectors (or dipoles) within the beam of light. As a result, the rotation of light and the generation of photoacoustic waves provide a means to gather comprehensive information about the optical characteristics and composition of the one or more test samples that are further utilized to measure the concentration of the chiral molecules non-invasively.
In accordance with an embodiment, the one or more test samples are bodily fluids or a portion of body tissue or a liquid solution with optical activity. The bodily fluids may include blood, saliva, plasma, urine, and the like. The optical activity refers to the property of the one or more test samples to change characteristics (such as plane of polarization) of the beam of light after passing through. As a result, the one or more test samples can be used for non-invasive measuring of the concentration of the chiral molecules effectively, accurately, and reliably.
In accordance with an embodiment, the chiral molecule is a sugar molecule. A chiral molecule refers to optically active molecules that do not superimpose a corresponding mirror image when the polarized light is passed through the corresponding molecules. Moreover, the symmetry of the chiral molecules enables the chiral molecules to rotate the plane of polarized light in a clockwise or anti-clockwise direction, known as optical activity. The enantiomers of the chiral molecules differ by properties and function. Examples of the chiral molecules may include, but are not limited to, glucoseazymes, deoxyribonucleic acid (DNA), amino acids, drugs, and the like. Moreover, the first state of polarization is a linear state, and the second state of polarization is a circular state. In other words, the orientation of the electromagnetic field vectors of the beam of light in the first state of polarization is different (i.e., the linear state) than the orientation of the electromagnetic field vectors in the second state of polarization (i.e., the circular state). Such change in orientation (i.e., from the linear state to the circular state) is caused due to the optical activity of the one or more test samples. In an implementation, in the first state of the polarization, the electromagnetic field vectors within the beam of light vibrate in a linear state. In another implementation, the first state of polarization is the vertical state. In yet another implementation, the first state of polarization is the circular state. Moreover, upon interaction with the chiral molecules in the one or more test samples, the first state of polarization changes to the second polarization state, and the second polarization state includes a circular or elliptic state that involves the rotation of the electric field vector of the light in a circular motion. Therefore, the utilization of specific polarization states provides a precise measurement of the concentration of the chiral molecules within the one or more test samples.
In accordance with an embodiment, the apparatus 102 further includes the light source 104 configured to emit the beam of light directly in the first state of polarization to reach to the one or more test samples. In an implementation, the beam of light is a monochromatic light beam with one wavelength corresponding to the maximum optical absorption of the chiral molecule being sensed. The direct emission in the first state of polarization enhances the efficiency and accuracy of the apparatus 102, thereby providing a beam of light in a desired state of polarization. Additionally, the emission of the beam of light directly in the first state of polarization eliminates the requirement of the additional devices, such as the one or more polarizing optics 106 that are further required to convent the unpolarized light into the beam of light with the first state of polarization.
In accordance with another embodiment, the apparatus 102 further comprises the light source 104 and the one or more polarizing optics 106. The light source 104 is configured to emit a beam of light in an unpolarized state towards the one or more polarizing optics 106. Moreover, the one or more polarizing optics 106 are configured to convert the beam of light from the unpolarized state to the polarized state corresponding to the first state of polarization to reach to the one or more test samples. Firstly, the light source 104 is configured to emit a beam of light, which is in the unpolarized state towards the one or more polarizing optics 106. Thereafter, the beam of light is converted to the polarized state (i.e., to the first state of polarization) through the one or more polarizing optics 106. The one or more polarizing optics 106 refer to optical components or devices, which are configured to control and manipulate a state of polarization of the beam of light. The one or more polarizing optics 106 may include, but are not limited to, one or more vertical polarizers, linear polarizers (such as Glan Taylor Crystal (GTC) polarizer), circular polarizers (such as Quarter Wave plate (QWP) polarizer), and the like. The one or more polarizing optics 106 allows a precise control over the orientation or characteristics of the beam of light to increase the accuracy of measurements performed by the apparatus 102. For example, the light source may be a neodymium-doped yttrium aluminium garnet (Nd: YAG) laser. Advantageously, the conversion of the beam of light from the unpolarized state to the polarized state enhances the flexibility to provide a convenient and efficient way to achieve the desired polarization conditions without relying on a specialized polarized light source, potentially enhancing the practicality and cost-effectiveness of the apparatus 102 for measuring the concentration of the chiral molecules within the one or more test samples.
In accordance with an embodiment, the apparatus 102 includes a beam splitter arranged at an output of the light source and an energy metering device. The beam splitter refers to an optical device configured to split the beam of light incident thereon. Examples of the beam splitter may include, but are not limited to, a plate beam splitter, cube beam splitter, polarizing beam splitter, dichroic beam splitter, non-polarizing beam splitter, and the like. An example of the arrangement of the beam splitter that is arranged at the output of the light source and the energy metering device is further described in detail, for example, in FIG. 2B.
In accordance with an embodiment, the beam splitter is configured to split the beam of light into a first beam and a second beam. The first beam is incident on the energy metering device, and the second beam is passed through the one or more polarizing optics 106. Moreover, the energy metering device is configured to measure the intensity of the beam of light in order to measure the energy level of the beam of light to normalize the photoacoustic electrical signals. In an implementation, the normalization of the photoacoustic electrical signals refers to a process that adjusts the variations in the intensity of the light source thereby, ensuring that the photoacoustic electrical signals are proportional to the actual energy content of the incident light. Moreover, such normalization is configured to enhance the accuracy and reliability of the photoacoustic measurements, providing a more consistent base for analyzing the optical characteristics of the one or more test samples. The second beam, which is passed through the one or more polarizing optics 106, is further passed through the one or more test samples placed within the test sample holder 108. Due to the optical activity of the one or more test samples, the first state of polarization of the second beam of light gets changed to the second state of polarization that further generates the photoacoustic waves. As a result, the first beam and the second beam are used to measure the concentration of the chiral molecules in the one or more test samples, taking into consideration the effect of high or low intensity of the beam of light, such as by normalizing the photoacoustic electrical signals.
Furthermore, the apparatus 102 includes the transducer 110 that is configured to receive the photoacoustic waves generated within the one or more test samples and convert the photoacoustic waves into photoacoustic electrical signals. Moreover, the photoacoustic electrical signals are a time series dataset, which is a function of depth in the one or more test samples. The transducer 110 refers to an electronic device, which is configured to convert the photoacoustic waves generated due to interaction between the beam of light and the one or more test samples into the photoacoustic electrical signals. In the apparatus 102, the transducer 110 is arranged adjacent to the test sample holder 108. Examples of the transducer 110 may include, but are not limited to, a focused ultrasonic transducer, a piezoelectric micromachined ultrasonic transducers (PMUT), a capacitive micromachined ultrasonic transducers (CMUT), a photoacoustic transducer, and the like. In an implementation, a focused ultrasound (US) transducer of 7.5 MHz can be used to acquire and record the photoacoustic electrical signals. The photoacoustic electrical signals are electrical signals that are generated as a result of the photoacoustic effect within the one or more test samples. Moreover, the change in the optical rotation of glucose by detecting the photoacoustic electrical signal changes (or photoacoustic rotation), the influence of different polarized state incidences on glucose rotation, and concentration estimation based on the changes in the photoacoustic rotation. For example, the photoacoustic electrical signals provide rotation information up to 3 mm, thereby surpassing the conventional optical imaging in order to allow an accurate glucose estimation at larger tissue depths. The photoacoustic electrical signals carry information about the absorption characteristics of the one or more test samples, including details about the concentration and distribution of the chiral molecules within the one or more test samples. The photoacoustic electrical signals are the time series dataset, which is a function of depth in the one or more test samples. In other words, the photoacoustic electrical signals are indicative of data recorded in a plurality of intervals of time at different depths of the one or more test samples. In other words, the photoacoustic electrical signals can be represented as a graphical representation indicating variation of amplitude against the linear depth of the one or more test samples. Advantageously, the time series dataset provides a spatial-temporal understanding of the chiral molecule distribution, offering a non-invasive measurement for detailed and depth-specific analysis.
Furthermore, the apparatus 102 includes the processor 112 communicatively coupled to the transducer 110. The processor 112 may refer to one or more individual processors, processing devices, and various elements associated with a processing device that may be shared by other processing devices. Additionally, the one or more individual processors, processing devices, and elements are arranged in various architectures for responding to and processing the instructions that drive the apparatus 102. Examples of the processor 112 may include but are not limited to, a hardware processor, a digital signal processor (DSP), a microprocessor, a microcontroller, a complex instruction set computing (CISC) processor, an application-specific integrated circuit (ASIC) processor, a reduced instruction set (RISC) processor, a very long instruction word (VLIW) processor, a state machine, a data processing unit, a graphics processing unit (GPU), and other processors or control circuitry. The processor 112 is configured to determine an angle of rotation between the first state of polarization and the second state of polarization based on the photoacoustic electrical signals. The angle of rotation between the first state of polarization and the second state of polarization represents a optical rotation of the first state of polarization to the second state of polarization. In an implementation, the angle of rotation is further used to detect the orientation of the electromagnetic field vectors of the beam of light in the first state of polarization and the orientation of the electromagnetic field vectors of the beam of light in the second state of polarization to determine the concentration of the chiral molecules in the one or more test samples. In an implementation, the processor is configured to analyze the photoacoustic electrical signals generated by the transducer 110 and approximately estimate the intensity of the beam of light incident on the one or more test samples and the intensity of the beam of light transmitted through the one or more test samples based Malus Law as given by equation (1):
I=I_0 cos^2??? (1)
where I indicate the intensity of the beam of light transmitted through the one or more test samples (i.e., the light with the second state of polarization), I_0 indicates the intensity of the beam of light incident on the one or more test samples (i.e., the light with the first state of polarization), and ? indicates the angle of rotation between the first state of polarization and the second state of polarization.
In accordance with an embodiment, the determination of the angle of rotation between the first state of polarization and the second state of polarization within the one or more test samples is based on a change in pressure observed in the photoacoustic waves as a function of depth estimated from the photoacoustic electrical signals. In other words, the processor 112 is configured to estimate the change in pressure observed from the photoacoustic waves to determine the angle of rotation as shown in the following equation (2) (by assuming optical absorption and Gruneisen parameter to be homogeneous):
P=P_0 cos^2??? (2)
where P indicates the pressure exerted due to photoacoustic waves during transmission of the beam of light through the one or more test samples (i.e., the light with the second state of polarization), P_(0?) indicates the pressure exerted due to photoacoustic waves during the incidence of the beam of light over the one or more test samples (i.e., the light with the first state of polarization), and ? indicates the angle of rotation between the first state of polarization and the second state of polarization. Further, the magnitude of the angle of rotation is calculated by equation (3):
??= cos^(-1)?v(P/P_0 ) (3)
The change in pressure in the photoacoustic waves is linked to the depth within the one or more test samples, providing a spatial dimension to the analysis. Therefore, by correlating the observed pressure changes with the depth information extracted from the photoacoustic electrical signals, the apparatus 102 can determine the angle of rotation between the first state of polarization and the second state of polarization, which, in turn, is indicative of the concentration of the chiral molecules within the one or more test samples.
Furthermore, the processor 112 is configured to determine the concentration of the chiral molecules in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization. After the determination of the angle of rotation between the first state of polarization and the second state of polarization, the rotation behaviour of the beam of light is observed to measure the concentration of the chiral molecules. The concentration of the chiral molecules in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization can be measured by using the equation (4) as given below:
C_p={¦(a_1 a^2+b_1 a+k_1,aa_T )¦ (4)
Where, a_T is the threshold value determined based on the variations with the rotation detected from photoacoustic experiments and C_p is the measured concentration of the chiral molecules from the calculated rotation (a) values.
In accordance with an embodiment, the processor 112 is configured to determine the change in pressure observed in the photoacoustic waves by deconvoluting the transducer 110 response from the photoacoustic electrical signals generated by the transducer 110. The deconvolution refers to a process of extracting or separating components of the photoacoustic electrical signals. The transducer 110 response refers to an additional signal generated by the transducer 110 due to the electrical sensor characteristics, apart from the photoacoustic electrical signals indicating the change in pressure. Due to the deconvoluting of the transducer response from the electrical signals, the processor 112 is configured to obtain the photoacoustic electrical signals to obtain accurate results during the measurement of the concentration of the chiral molecules. Beneficially, due to deconvoluting the transducer response from the electrical signals, the processor is configured to obtain the photoacoustic electrical signals that can be further utilized to measure the concentration of the chiral molecules accurately.
Advantageously, the apparatus 102 is designed for non-invasive measuring of the concentrations of the chiral molecules in the one or more test samples efficiently, effectively, and accurately. The test sample holder 108 receives a polarized beam of light that is rotated by the chiral molecules in the samples, generating photoacoustic waves. The optical rotation of the beam of light that is from the first state of polarization to a second state of polarization provides a precise analysis of the chiral molecule concentrations in a non-invasive manner, offering depth-specific information crucial for accurate concentration measurement. The transducer 110 converts the photoacoustic waves within the one or more test samples into time-series photoacoustic electrical signals, providing a depth-dependent dataset (i.e., a time-series dataset) to allow spatial-temporal analysis of the one or more test samples. The processor 112 is configured to determine the angle of rotation between the first state of polarization and the second state of polarization. Further, by analyzing the pressure changes in the photoacoustic waves, the processor 112 is configured to calculate the angle of rotation, allowing a precise determination of the concentration of the chiral molecules. The apparatus 102 is configured to analyze bodily fluids, body tissue, or optically active liquid solutions, thereby providing a non-invasive way of measuring the concentration of the chiral molecules. As a result, the apparatus 102 provides a non-invasive and depth-specific measurement of the concentration of the chiral molecules with enhanced accuracy and reliability, offering a painless and convenient way of monitoring the level of the chiral molecules in the human body.
Referring to FIG. 2A there is shown a diagram of an apparatus for measuring the concentration of the chiral molecules, in accordance with an embodiment of the present disclosure. FIG. 2A is explained in conjunction with elements from FIG. 1. With reference to FIG. 2A, there is shown a diagram 200A of the apparatus 102 that represents the light source 104, the one or more polarizing optics 106, the test sample holder 108, and the transducer 110 arranged sequentially. Furthermore, the processor 112 is communicatively coupled to the transducer 110. The apparatus 102 is represented by a dashed box, which is used for illustration purposes only and does not form a part of the circuitry.
In operation, the one or more polarizing optics 106 are configured to receive the beam of light from the light source 104 and convert the beam of light to the first state of polarization. Further, the beam of light having the first state of polarization passes through the one or more test samples placed within the test sample holder 108. Due to the optical activity of the one or more test samples, the first state of polarization of the beam of light gets converted into the second state of polarization. Due to the change in the state of polarization, the one or more test samples generate the photoacoustic waves. Furthermore, the transducer 110 is configured to receive the photoacoustic waves generated within the one or more test samples and convert the photoacoustic waves into the photoacoustic electrical signals. Moreover, the photoacoustic electrical signals are a time series dataset, which is a function of depth in the one or more test samples that are indicative of data recorded in a plurality of intervals of time at different depths of the one or more test samples. In addition, the processor 112 is configured to determine an angle of rotation between the first state of polarization and the second state of polarization based on the photoacoustic electrical signals. The processor 112 is configured to determine the orientation of the electromagnetic field vectors of the beam of light in the first state of polarization and the orientation of the electromagnetic field vectors of the beam of light in the second state of polarization to obtain the angle of rotation. Thereafter, the processor 112 is configured to determine the concentration of the chiral molecule in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization. Finally, the processor 112 is configured to correlate the angle of rotation (or photoacoustic rotation) to measure the concentration of the chiral molecules within the one or more test samples accurately and reliably.
Referring to FIG. 2B, there is shown another diagram of an apparatus, in accordance with another embodiment of the present disclosure. FIG. 2B is described in conjunction with elements from FIGs. 1 and 2A. With reference to FIG. 2B, there is shown a diagram 200B of the apparatus 102. The apparatus 102 further includes an aperture 202, a long pass dichroic mirror 206, an energy meter device 204, a gran-Taylor crystal polarizer 208, a quarter wave plate 210, a first broadband mirror 212A, a second broadband mirror 212B, a magnetic stirrer 214, a syringe 216, an amplifier 218, and a digital storage oscilloscope (DSO) 220.
In operation, the light source 104 is configured to emit a beam of light towards the test sample holder 108. The aperture 202 is arranged in such a manner that the beam of light which is emitted through the light source 104 is passed through the aperture 202 in order to reduce the diameter of the beam of light. Furthermore, the long pass dichroic mirror 206 (or a beam splitter) is configured to split the beam of light into a first beam and a second beam. Thereafter, the first beam is incident on an energy metering device 204, and the second beam is passed through the one or more polarizing optics 106, such as the gran-Taylor crystal polarizer 208 (i.e., for linear beam light) and the quarter wave plate 210 (i.e., for a circular beam of light). Moreover, the energy metering device 204 is configured to measure the intensity of the beam of light based on the intensity of the first beam in order to measure the energy level of the beam of light to normalize the photoacoustic electrical signals. As a result, the effect of high or low intensity of the beam of light can be handled, such as by normalizing the photoacoustic electrical signals. Furthermore, the beam of light is passed through the first broadband mirror 212A and the second broadband mirror 212B, which is configured to adjust the alignment of the beam of the light and further pass the beam of light to the test sample holder 108. The test sample holder 108 includes a glucose solution (added by the syringe 216) and is placed on the magnetic stirrer 214 in order to ensure homogeneity throughout the measuring of the concentration of the molecules. Furthermore, the transducer 110 is configured to receive the photoacoustic waves generated within the one or more test samples and convert the photoacoustic waves into photoacoustic electrical signals that are passed to the DSO 220 after the amplification through the amplifier 218 for further processing. Thereafter, the processor 112 is configured to determine an angle of rotation between the first state of polarization and the second state of polarization based on the photoacoustic electrical signals and further determine the concentration of the chiral molecules in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization. As a result, the apparatus 102 is configured to determine the concentration of the chiral molecules accurately and reliably.
FIGs. 3A, 3B, 3C, and 3D are graphical representations depicting the calculation of photoacoustic rotation from a time-series photoacoustic electrical signals, in accordance with an embodiment of the present disclosure. With reference to FIG. 3A, there is shown a graphical representation 300A depicting an exemplary representation of time-series photoacoustic electrical signals obtained using the transducer 110 (shown in FIG. 1). With reference to FIG. 3B, there is shown a graphical representation 300B, depicting an exemplary photoacoustic electrical signal in the frequency domain. With reference to FIG. 3C, there is shown a graphical representation 300C depicting an exemplary representation of a transducer response (i.e., the response obtained from the transducer 110 of FIG. 1). With reference to FIG. 3D, there is shown a graphical representation 300D depicting an exemplary representation of a deconvolved output. Specifically, the graphical representation 300A, the graphical representation 300B, the graphical representation 300C, and the graphical representation 300D depict the calculation of the photoacoustic rotation from the photoacoustic electrical signals.
The graphical representation 300A represents the time series photoacoustic electrical signals that are obtained from the digital storage oscilloscope (i.e., the DSO 220 of FIG. 2). The time series photoacoustic electrical signals are expressed as an amplitude (a.u) in an ordinate axis and are mapped to the depth, which is expressed as milli meter (mm) units in an abscissa axis. Furthermore, the time-series data is mapped to depth after the deconvolution, which is performed in the frequency domain. The graphical representation 300B represents the frequency domain representation of the acquired time-series data. Moreover, the photoacoustic magnitude spectrum expressed as an amplitude (a.u) in an ordinate axis with respect to the frequency that is expressed in hertz in an ordinate axis. Moreover, the graphical representation 300C represents the transducer response that affects the photoacoustic electrical signals. The photoacoustic electrical signals are deconvolved with the transducer response (as shown in the graphical representation 300C) for selecting the P and P_(0?)from the time-series data across depth. A deconvolved output is obtained (as shown in the graphical representation 300D) that is further utilized to choose the P and P_(0?) from the photoacoustic time-series measurements. The graphical representation 300D represents the photoacoustic electrical signals that are expressed as an amplitude (a.u) in an ordinate axis and is mapped to the depth, in an abscissa axis. Finally, the rotation (i.e., the angle of rotation) is calculated by using equation (3), which is further used for the measurement of the concentration of the chiral molecules in the one or more test samples, such as by utilizing the equation (4), as described in detail in FIG. 1. As a result, the accurate, reliable, and efficient measurement of the concentration of the chiral molecules can be performed by the apparatus 102.
FIG. 4A is a graphical representation of a calculated rotation varying with concentration for a vertical incidence in an aqueous chiral molecular solution, in accordance with an embodiment of the present disclosure. With reference to FIG. 4A, there is shown a graphical representation 400A that depicts a rotation varying with concentration for a vertical incidence in an aqueous chiral molecular solution. The concentration is expressed in milligrams per deciliter (mg/dL), ranging from 50 to 400 in an abscissa axis. The rotation is expressed in radians (rad) ranging from 0.8 to 1 in an ordinate axis for the considered path length. The graphical representation 400A represents the rotation of the polarized light in the aqueous solution, which increases linearly with an increase in concentration (e.g., from 0 mg/dL to 200 mg/dL). However, the rate of increase of the light decreases as soon as the concentration approaches a saturation point (e.g., from 200 mg/dL to 300 mg/dL). Furthermore, the rotation of polarized light becomes non-linear due to the interaction of the chiral molecules with each other (e.g., from 300 mg/dL to 400 mg/dL). As a result, the rotation varying with concentration for the vertical incidence can be calculated for the aqueous solution.
FIG. 4B is a graphical representation of a calculated rotation varying with concentration for a vertical incidence in a bovine serum albumin solution, in accordance with an embodiment of the present disclosure. With reference to FIG. 4B, there is shown a graphical representation 400B that depicts a rotation varying with concentration for a vertical incidence in a bovine serum albumin chiral molecular solution. The rotation is expressed in radians (rad) ranging from 0.99 to 1.05 in an ordinate axis. The concentration is expressed in milligrams per deciliter (mg/dL), ranging from 100 to 350 in an abscissa axis. The graphical representation 400B represents that the rotation for lower concentrations shows a slight non-linear behaviour while higher concentrations show a linear increase in photoacoustic signal as a function of concentration.
FIG. 5A is a graphical representation of Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a vertical incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5A, there is shown a graphical representation 500A that depicts experimental data for Clarke’s error grid analysis (CEGA) in the vertical incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an ordinate axis.
FIG. 5B is a graphical representation of Clarke’s error grid analysis (CEGA) for the bovine serum albumin dissolved glucose solution for the vertical incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5B, there is shown a graphical representation 500B that depicts experimental data for Clarke’s error grid analysis (CEGA) in the bovine serum albumin (BSA) solution for a vertical incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an ordinate axis.
FIG. 5C is a graphical representation of Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a linear incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5C, there is shown a graphical representation 500C that depicts an experimental data for Clarke’s error grid analysis (CEGA) in the linear incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL) ranging from 0 to 400 in an ordinate axis.
FIG. 5D is a graphical representation of Clarke’s error grid analysis (CEGA) for the bovine serum albumin glucose solution for the linear incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5D, there is shown a graphical representation 500D that depicts an experimental data for Clarke’s error grid analysis (CEGA) in a bovine serum albumin (BSA) solution for the linear incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL) ranging from 0 to 400 in an ordinate axis.
FIG. 5E is a graphical representation of Clarke’s error grid analysis (CEGA) for the aqueous glucose solution for a circular incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5E, there is shown a graphical representation 500E that depicts an experimental data for Clarke’s error grid analysis (CEGA) in the aqueous solution for the circular incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an ordinate axis.
FIG. 5F is a graphical representation of Clarke’s error grid analysis (CEGA) for the bovine serum albumin glucose solution for the circular incidence, in accordance with an embodiment of the present disclosure. With reference to FIG. 5F, there is shown a graphical representation 500F that depicts an experimental data for Clarke’s error grid analysis (CEGA) in the bovine serum albumin (BSA) solution for the circular incidence. The reference concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an abscissa axis. The predicted concentration is expressed in milligrams per deciliter (mg/dL), ranging from 0 to 400 in an ordinate axis.
Modifications to embodiments of the present disclosure described in the foregoing are possible without departing from the scope of the present disclosure as defined by the accompanying claims. Expressions such as “including”, “comprising”, “incorporating”, “have”, “is” used to describe, and claim the present disclosure are intended to be construed in a non-exclusive manner, namely allowing for items, components, or elements not explicitly described also to be present. Reference to the singular is also to be construed to relate to the plural. The word “exemplary” is used herein to mean “serving as an example, instance, or illustration”. Any embodiment described as “exemplary” is not necessarily to be construed as preferred or advantageous over other embodiments and/or to exclude the incorporation of features from other embodiments. The word “optionally” is used herein to mean “is provided in some embodiments and not provided in other embodiments”. It is appreciated that certain features of the present disclosure, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the present disclosure, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable combination or as suitable in any other described embodiment of the disclosure. , Claims:1. An apparatus (102) for measuring concentration of chiral molecules, the apparatus (102) comprising:
a test sample holder (108) to hold one or more test samples configured to receive a beam of light in a first state of polarization, wherein the one or more test samples rotate the beam of light from the first state of polarization to a second state polarization and concomitantly generates photoacoustic waves;
a transducer (110) configured to receive the photoacoustic waves generated within the one or more test samples and convert the photoacoustic waves into photoacoustic electrical signals, wherein the photoacoustic electrical signals is a time series dataset which is a function of depth in the one or more test samples; and
a processor (112) communicatively coupled to the transducer (110), wherein the processor (112) is configured to determine an angle of rotation between the first state of polarization and the second state of polarization based on the photoacoustic electrical signals and determine the concentration of the chiral molecules in the one or more test samples based on the angle of rotation between the first state of polarization and the second state of polarization.
2. The apparatus (102) as claimed in claim 1, wherein the determination of the angle of rotation between the first state of polarization and the second state of polarization within the one or more test samples is based on a change in pressure observed in the photoacoustic waves as a function of depth estimated from the photoacoustic electrical signals.
3. The apparatus (102) as claimed in claim 2, wherein the processor (112) is configured to determine the change in pressure observed in the photoacoustic waves by deconvoluting a transducer (110) response from the photoacoustic electrical signals generated by the transducer (110).
4. The apparatus (102) as claimed in claim 1, wherein the one or more test samples are bodily fluids or a portion of body tissue or a liquid solution with optical activity.
5. The apparatus (102) as claimed in claim 1, wherein the chiral molecule is sugar molecule, and wherein the first state of polarization is a linear state, and the second state of polarization is a circular state.
6. The apparatus (102) as claimed in claim 1, wherein the apparatus (102) further comprises a light source (104) configured to emit the beam of light directly in the first state of polarization to reach to the one or more test samples.
7. The apparatus (102) as claimed in claim 1, wherein the apparatus (102) further comprises a light source (104) and one or more polarizing optics (106), wherein the light source (104) is configured to emit the beam of light in an unpolarized state towards the one or more polarizing optics, and wherein the one or more polarizing optics are configured to convert the beam of light in the unpolarized state into a polarized state corresponding to the first state of polarization to reach to the one or more test samples.
8. The apparatus (102) as claimed in claim 7, wherein the apparatus (102) comprises a beam splitter arranged at an output of the light source (104) and an energy metering device (206).
9. The apparatus (102) as claimed in claim 8, wherein the beam splitter is configured to split the beam of light into a first beam and a second beam, the first beam is incident on the energy metering device (204) and the second beam is passed through the one or more polarizing optics (106), and wherein the energy metering device (204) is configured to measure the intensity of the beam of light based on the intensity of the first beam in order to measure the energy level of the beam of light to normalize the photoacoustic electrical signals.