Patent Grant
9518914
The present invention relates to system and method adapted to expedite a determination of the required treatment based on a point-of-care measurement of a bodily fluid sample.
A large portion—in excess of 8 percent in 2009—of funds available under the Medicare program is directed towards the treatment and medications of End Stage Renal Disease (ESRD) patients, which emphasizes the significance of this area of medical treatment. The success of the sought treatments, however, remains substantially low as evidenced by the related statistical data. According to 1999-2004 National Health and. Nutrition Examination Survey (NHANES), the prevalence of chronic kidney disease (CKD) in the US adult population was about 16.8% of the overall U.S. population 20 years and older, which indicated a significant increase as compared to the numbers determined in 1988, for example. For CKD patients with ESRD, kidney replacement or dialysis to preserve any residual renal function is commonly required. Millions of people worldwide are receiving renal replacement therapy, and this number grows at an annual rate of about 8%. Treatments for the ESRD account for $39.5 billion US dollars in both public and private spending.
The examination of bodily fluid samples provides support for patient care to-date. For example, hemodialysis (HD) and peritoneal dialysis (PD) are the currently employed methods to treat advanced and permanent kidney failure. The PD patients account for about 7% of all dialysis patients in the USA as compared to outside the US (Canada, Mexico, Europe, Asia) where this number is much higher (between 35% and 80%). The PD treatment is recognized to be significantly less expensive than the HD treatment per year per patient. Incentives are emerging to keep patients on PD therapy. For example, a patient may qualify immediately for the PD coverage, whereas the HD coverage does not begin until after a 90 day grace period. Accordingly, the HD may be considered inconvenient by many patients, who would find it hard to travel to a HD center several times per week and spend between 3 and 5 hours per visit on an HD procedure that requires support from a healthcare team. Nevertheless, both the HD and PD procedures re found to be quite useful.
Home-based therapy, which includes home hemodialysis and PD, would provide an advantageous alternative to the existing implementations of the HD and PD due to lower cost and higher patient satisfaction. Barriers to home-based implementation of PD are defined, in part, by the risk of recurring peritonitis or inflammation of the peritoneum that diminishes the filtering properties of the peritoneal membrane and potentially reduces the time-window available for kidney transplant. Peritonitis is clinically defined as the occurrence of a turbid effluent in the dialysate containing more than 100 white blood cells (WBCs) per microliter, of which more than 50% are neutrophils The PD patients exchange the PD fluid 2-5 times a day. When the PD procedures are implemented as home-based procedures, patients are expected to observe the cloudiness/turbidity of their dialysate at every exchange and initiate a call to their caregivers if they observe cloudiness in the fluid. However, interpretations based on cloudiness of the dialysate do not provide the accurate means to predict peritonitis
Accordingly, there exists a need in a practical modality overcoming the above-described deficiencies.
Embodiments of the present invention provide a system for at least one of identifying and counting target cells in a bodily fluid sample, the system including an element with a network of microfluidic channels, a light source, an optical detector positioned adjacently to the element without an optical component therebetween such that the optical detector is adapted to receive light through the element, and a non-transitory computer readable medium having computer readable program code for counting target cells in a fluid dialysis sample. The dialysis sample may include but not limited to a hemodialysis or peritoneal dialysis sample. The program code includes a series of computer readable program steps to effect (i) acquiring data representing a gray-scale image (or color image, or multi- or hyperspectral image) of said network formed on a surface of the optical detector in light that has traversed the network of microfluidic channels; and (ii) processing the acquired data to obtain a visually-enhanced image using state-of-the-art techniques of image enhancement to standardize the input image, as well as effectuating a feature detection to identify structural features of the carrier in which the dialysis sample is contains, and using shape detection and morphology identification algorithm to perform cell identification and count in the dialysis sample. In one example, the processing of data may include (iia) converting the acquired data to data representing a gray-scale image of the network of channels; (iib) at least one of filtering in a frequency domain and filtering in a spatial domain of so converted data; and (iic) when a channel of the network contains a fluidic sample with identified biological cells, counting the cells in relation to the channel parameters and a predefined threshold value to determine a count value.
Embodiments of the invention also provide a system for at least one of identifying and counting target cells in a bodily fluid sample, which system includes a plurality of microfluidic channels; a light source positioned to transmit light through this plurality of channels; an optical detector positioned adjacent to the plurality of channels to receive light from the light source after passing through the plurality of channels such as to form an irradiance distribution representing the sample contained in at least one of the plurality of channels at the optical detector; and one or more processors having thereon operational computer code configured to perform one or more steps of a method for at least one of identifying and counting target cells in the sample. Such method includes (i) acquiring data representing an initial image of the plurality of channels formed on a surface of the optical detector in light that has traversed the channels; (ii) converting the acquired data to monochrome image data representing the plurality of microfluidic channels; and (iii) processing the monochrome image data by filtering the data in at least one of a frequency domain and a spatial domain. The method may further include a step of identifying target cells from the processed monochrome image data and, optionally, counting the identified target cells.
Embodiments of the invention additionally provide an article of manufacture comprising a microprocessor and a computer readable medium that includes computer readable program code for counting target cells in a fluid peritoneal dialysis sample contained in a channel of a microfluidic system. The system includes a microfluidic chip having one or more of channels; an optical detector adjacent to the microfluidic chip; and a light source adapted to transmit light through the channel onto the optical detector such as to form an image in the fluid peritoneal dialysis sample at the detector in absence on an imaging optical component. The computer readable program code includes a series of program steps to enable counting of the target cells based at least in part on conversion of data representing the formed image from color scale to gray scale. Additionally or alternatively, the computer readable program code further comprises steps to enable the counting of cells based on a probability of the target cells to be located near a surface of the channels and a likelihood of bond formation between so located cells and receptors.
Embodiments of the invention additionally provide a system for at least one of identifying and counting target cells in a bodily fluid sample. The system includes one or more computer processors and a computer-readable medium comprising computer code which is configured to perform, when used to operate one or more computer processors, one or more steps of a method for at least one of identifying and counting target cells in a bodily fluid sample. The system includes a microfluidic chip having one or more microfluidic channels; an optical detector adjacent to the microfluidic chip; and a light source adapted to transmit light through a microfluidic channels onto the optical detector such as to form an irradiance distribution representing the bodily fluid sample at the optical detector in absence of an optical component forming an optical conjugate of the fluid sample at the detector. In such a system, the step(s) of the method are effectuated based at least in part on conversion of data representing the formed irradiance distribution to a monochrome scale.
Embodiments additionally provide a method for identifying cells contained in a fluid peritoneal dialysis sample. Such method includes (i) receiving data representing an image of neutrophils formed in light, that has traversed a microfluidic channel containing said fluid sample, without the use of an optical imaging component; and (ii) processing the received data to determine a count of the neutrophils based on probability of the cells to be located near a surface of the microfluidic channel and likelihood of bond formation between so located cells and receptors. The method may further include determining a probability of a steady-state adhesion of the neutrophils to the surface of the microfluidic channel. Alternatively or in addition, the method may include generating visually-perceivable triggering indicator when the determined count exceeds a threshold value adjustable based on a user input.
Embodiments additionally provide a method for at least one of identifying and counting target cells in a bodily fluid sample, which method includes (i) providing a system comprising a plurality of microfluidic channels, a light source configured to transmit light through such plurality of channels, and an optical detector configured to receive light from the light source after passing through the plurality of channels such as to form an irradiance distribution representing the fluid sample at the detector; (ii) arranging the bodily fluid sample in at least one of the plurality of channels; (iii) illuminating the plurality of channels with the light source; (iv) acquiring data representing an initial image of the plurality of channels at the detector in transmission of light through at least one channel; (iv) converting the acquired data to monochrome image data; (v) processing the monochrome image data by filtering these data in at least one of a frequency domain and a spatial domain; (vi) identifying target cells from the processed monochrome image data; and optionally counting the identified target cells.
Embodiments additionally provide a non-transitory tangible computer readable medium having stored thereon computer code operational on one or more processors of a computer system to perform a method for at least one of identifying and for counting target cells contained in a bodily fluid sample, which method comprises acquiring data representing an initial image of at least one of a plurality of microfluidic samples on a surface of an optical detector in light from a light source that has passed through the at least one of the plurality of channels. The method additionally includes converting the acquired data to monochrome image data and processing the monochrome image data by filtering these data in at least one of a frequency domain and a spatial domain. The method further includes identifying target cells from the processed monochrome image data and, optionally, counting the identified target cells.
The invention will be more fully understood by referring to the following Detailed Description in conjunction with the Drawings, of which:
Hemodialysis (also referred to as haemodialysis, or HD) is a method that is used to achieve the extracorporeal removal of waste products such as creatinine and urea and free water from the blood when the kidneys are in a state of renal failure. Peritoneal dialysis is used as an alternative to HD, though it is far less commonly used. While the PD, as compared to traditional HD, provides higher quality of care, both procedures are available and provide ease of access to the patients. It is understood that, while in the disclosure below, the reference is made to PD, such reference is made only to make the disclosure concise and that the use of HD fluid or any other bodily fluid as a sample for analysis discussed below was considered to be within the scope of the invention.
A recognized clinical barrier in peritoneal dialysis is the risk of peritonitis, i.e. inflammation of peritoneum. Peritonitis is clinically defined as the occurrence of a turbid dialysate containing more than 100 white blood cells (WBCs) per microliter of which more than 50% are neutrophils. As infection progresses, a substantial increase in WBCs results in higher degree of opaqueness of the peritoneal dialysate. However, at the early stages of infection the change in the turbidity is not visually detectable.
The decision-making on whether the infection has occurred is currently based on assessment, by the patient himself, of a degree of opaqueness and visually perceived cloudiness of the bodily fluid such as the dialysate, which is understandably subjective and, at least for that reason, is not quite adequate to monitor peritonitis. Clinically, the WBCs and neutrophil counts are used to assess the occurrence of peritonitis. On the other hand, since a cell counting platform is not accessible at the point-of-care (POC), when the bodily fluid or dialysate appears turbid, it is considered to be an indication of a potential infection and patients are expected to initiate a call to their caregivers followed by an immediate visit to the doctor's office or emergency room. In reference to Table 1, the observations performed by patients can, overall, be misleading causing unnecessary emergency room visits, hospitalizations, and subsequent doctor office visits, which could have been avoided with reliable bedside testing.
The above-described situation is exacerbated by the facts that (i) the bodily fluid or dialysate's cloudiness (turbidness) can be caused by other reasons (for example, drugs such as manidipine hydrochloride, a dihydropyridine-type calcium channel blocker) that do not necessarily indicate peritonitis, and (ii) the lack of appropriate quantitative monitoring technology complicates the monitoring of the health status of a HD/PD patient. Overall, there exists a not addressed yet, unmet clinical need for rapid and quantitative monitoring of a dialysate to determine the risk of infection.
To address this clinical need, embodiments of the present invention provide a disposable bodily fluid microchip (for example, an HD/PD microchip) and a corresponding method for operation of such microchip to enable rapid quantification of neutrophils in a dialysate to monitor the health status of an HD/PD patient. In a pilot study, neutrophil microchip counts in dialysates of 20 HD/PD patients were obtained (ranging from 16±2 to 842±29 neutrophils per 100 microliters) over a time period of up to 190 days. An HD/PD microchip was operable to successfully determine the status of the patients. The proposed embodiments are broadly applicable for rapid quantitative analysis of body fluids at the bedside/point of care location, covering a broad range of diseases that require continuous or repetitive monitoring. References throughout this specification to “one embodiment,” “an embodiment,” “a related embodiment,” or similar language mean that a particular feature, structure, or characteristic described in connection with the referred to “embodiment” is included in at least one embodiment of the present invention. Thus, appearances of the phrases “in one embodiment,” “in an embodiment,” and similar language throughout this specification may, but do not necessarily, all refer to the same embodiment. It is to be understood that no portion of disclosure, taken on its own and in possible connection with a figure, is intended to provide a complete description of all features of the invention.
In addition, the following disclosure may describe features of the invention with reference to corresponding drawings, in which like numbers represent the same or similar elements wherever possible. In the drawings, the depicted structural elements are generally not to scale, and certain components are enlarged relative to the other components for purposes of emphasis and understanding. It is to be understood that no single drawing is intended to support a complete description of all features of the invention. In other words, a given drawing is generally descriptive of only some, and generally not all, features of the invention. A given drawing and an associated portion of the disclosure containing a description referencing such drawing do not, generally, contain all elements of a particular view or all features that can be presented is this view, for purposes of simplifying the given drawing and discussion, and to direct the discussion to particular elements that are featured in this drawing. A skilled artisan will recognize that the invention may possibly be practiced without one or more of the specific features, elements, components, structures, details, or characteristics, or with the use of other methods, components, materials, and so forth. Therefore, although a particular detail of an embodiment of the invention may not be necessarily shown in each and every drawing describing such embodiment, the presence of this detail in the drawing may be implied unless the context of the description requires otherwise. In other instances, well known structures, details, materials, or operations may be not shown in a given drawing or described in detail to avoid obscuring aspects of an embodiment of the invention that are being discussed. Furthermore, the described single features, structures, or characteristics of the invention may be combined in any suitable manner in one or more further embodiments.
Moreover, if the schematic flow chart diagram is included, it is generally set forth as a logical flow-chart diagram. As such, the depicted order and labeled steps of the logical flow are indicative of one embodiment of the presented method. Other steps and methods may be conceived that are equivalent in function, logic, or effect to one or more steps, or portions thereof, of the illustrated method. Additionally, the format and symbols employed are provided to explain the logical steps of the method and are understood not to limit the scope of the method. Although various arrow types and line types may be employed in the flow-chart diagrams, they are understood not to limit the scope of the corresponding method. Indeed, some arrows or other connectors may be used to indicate only the logical flow of the method. For instance, an arrow may indicate a waiting or monitoring period of unspecified duration between enumerated steps of the depicted method. Without loss of generality, the order in which processing steps or particular methods occur may or may not strictly adhere to the order of the corresponding steps shown.
The invention as recited in claims appended to this disclosure is intended to be assessed in light of the disclosure as a whole, including features disclosed in prior art to which reference is made.
As was already alluded to above, while in the examples discussed below, the references are made only to PD, such references are made only for the sake of keeping the description concise and simplified, and use of HD procedure and HD fluid sample or any other bodily fluid as a sample for analysis intended to be within the scope of the invention.
In reference to
In the following portion of the present disclosure, in reference to
The diagram A of
To complement an algorithm of the invention (referred to herein as the HVC method), an embodiment of the computer program product of the invention includes program code for processing image data, received by the electronic data-processing computer circuitry (which maybe referred to as a processor, for short) after an initial phase of image restoration, with the use of frequency domain (FD) operations. After the FD-processing, the data are re-processed using spatial domain (SD) operations to produce a final result based on an intersection of the two outputs. The computer program product may include program codes to effectuate the following steps:
The above-mentioned steps of an embodiment of the image-processing algorithm of the invention are described below.
Automatic and/or Manual Selection of Channels on a Chip.
It may be required to count the cells in each of the channels 100a of the chip 100 of
Fully Automatic Mode.
This mode is built-in for the mass processing of images taken on a particular chip. In further reference to
Semi-Automatic Mode.
In this mode, and in reference to image A of
Fully Manual Mode.
In this mode, the computer program product enables the processor to allow the user to re-sizably and movably mark any region in an image (whether rectangular or square in shape, such as the area 430 of image B of
Image Restoration.
If an acquired image has low contrast, a normalization and/or standardization procedure is performed to ensure that an image of a cell stands out against the background. In reference to an image 510 of
Frequency Domain Band-Pass Filtering.
As a result of the boosting of high-frequency characteristics of the image 514, the 2D Fourier Transform 524 of the high-frequency-boosted filtered image 518 may exhibit a “halo” 528 shown in
While the frequency domain band-pass filtering emphasizes the cells and attenuates other unwanted elements of the image, cells are not the only contributors to the “halo” and some amount of noise remains. The noise-producing elements can include, for example, air-bubbles, fibers, and fine structures from the sample that are not cells. Instead of trying to handle each contribution to image noise, an embodiment of the HCC method of the invention takes advantage of the facts that (i) the cells of interest are almost always roundish and have substantially the same diameter; (ii) the imaging is carried out with the same system; (iii) the chip is always positioned at the substantially the same distance from the CCD. This makes it possible to use morphology of the cells of interest and identify round objects of a certain diameter, as discussed further below.
Detection of Round Objects Using Matched Filtering.
At this stage, the imaging data representing the high-boost filtered image 518 are used as input again. The image 518 is first converted into a binary image and then convolved with a template of a “disk”.
Fine Tuning the Matches.
Incorporating User Feedback to Update the Threshold Specifying which Objects should be Counted as Cells.
The final result depends on the value of the threshold that was specified. Once the counting of cells is accomplished, each valid cell is marked on the original image and displayed to the user for visual confirmation. At this point, the user has the ability to adjust the value of the threshold and, therefore, the results. The number of cells is displayed on the figure window and is dynamically updated. The higher the threshold, the fewer the number of points identified as cells but these have higher likelihood of actually being cells. The lower the threshold, more points are identified as cells but it the number of false positives generally increase.
The overall image processing algorithm described above is summarized in the flowchart of
In the following portion of the disclosure, in reference to
To design microchannels 100a of an embodiment 100 of
These probabilities include (1) the probability that the cells in questions are located near the surface of the microchannel 100a and margination (if any) of cells towards equilibrium zones, which can potentially feed the cell population near the channel surface, as shown in the graph of the diagram B; and (2) the likelihood of bond formation between the cells locates near the channel surface and the receptors, as shown in the graph of the diagram C of
where yWBC is the vertical distance of CD66b+ neutrophils, dyWBC/dt is the margination velocity, yWBC* is the equilibrium vertical distance, a is the radius of CD66b+ neutrophils, ρ0 and ε0 are fluid density and viscosity. At the next step, the average margination velocity and average flow velocities are calculated as um=[∫0h(dyWBC/dt)dy]/h, and uf=[∫0hu(y)dy]/h, respectively. Following this calculating, time scales are compared by t*=(h/um)/(L/uf).
As time scale ratio of margination and flow is >>1 (t*˜100), initial distribution of neutrophils will be the determining factor. Here, we simply assume that cells will be normally distributed across the flow as:
where μ is the mean location and σ−2 is the variance of cell distribution. In further reference to the diagram B of
The neutrophils were adhered to the bottom surface of the microchannel. The effective fluidic forces that can potentially dislodge neutrophils are given by F=6πalμSFs and M=6πa3μSTs where l is the separation distance to the wall, μS is the shear stress at the wall, Fs and Ts are shape-dependent coefficients. The shear stress on microchannel surface, τw, can be calculated as:
Σw=6μQ/(wh2) (4)
Here, shear stresses are 0.0078 Pa for h=80 μm and 0.02 Pa for h=50 μm. Accordingly, and in further reference to the diagram C of
where mr and ml are the receptor and ligand densities, respectively; Ka0 is the association constant at zero load of the ligand-receptor pair; Ac is the contact area; λ is the characteristic length of the ligand-receptor bonds; kb is the Boltzmann constant; Fdis is the dislodging force acting per unit ligand-receptor pair; γ is the cell aspect ratio; and T is the temperature.
Finally, and in reference to the diagram E of
Referring again to
200 proofs of ethanol (EtOH), for dilutions and washing of channels, and dimethyl sulfoxide (DMSO), the solvent for GMBS stock solution, were purchased from Sigma-Aldrich Chemical Company (St. Louis, Mo.). 3-mercaptopropyl trimethoxysilane (3-MPS), a silanization agent, was also purchased from Sigma-Aldrich Chemical Company (St. Louis, Mo.). N-y-maleimidobutyryloxy succinimide ester (GMBS), a coupling agent, was purchased from Pierce Biotechnology (Rockford, Ill.). 1× phosphate buffered saline (PBS) solution, for dilution of aqueous reagents and washing, was purchased from Gibco (Grand Island, N.Y.). NeutrAvidin, a functional protein for biotin binding, was purchased from Fisher Scientific (Fair Lawn, N.J.). Lyophilized albumin from bovine serum (BSA), for blocking nonspecific bindings/interactions, was purchased from Sigma-Aldrich Chemical Company (St Louis, Mo.). Biotinylated anti-human carcinoembryonic antigen-related cell adhesion molecule 8 (CEACAM-8) antibody, used for the capture of neutrophils in clinical PD samples, was purchased from R&D Systems (Minneapolis, Minn.).
Materials for Neutrophil Capture and Analysis.
The syringe pump, used for passing the PD sample through the microfluidic chip, was purchased from SyringePump.com (Farmingdale, N.Y.). The 1 mL Luer Lock syringes, used to inject the PD fluid through the microfluidic chip, were purchased from BD Biosciences (Franklin Lakes, N.J.). The 0.01″ inner diameter nylon tubing, used to connect the syringes to the microfluidic chip, was purchased from Cole-Parmer (Vernon Hills, Ill.). The microfluidic chip was cleaned with Zeiss Lens Cleaner, purchased from Carl Zeiss Optical Inc. (Cleveland, Ohio). The charge-couples device (CCD), used for imaging of the chip to quantify neutrophil capture, was purchased from Imperx Inc. (Boca Raton, Fla.) and incorporated into the ‘black box’ with an LED light source with 86.9 kΩ resistance and 2.3V power source.
Solution Preparation.
Once the microfluidic chip was assembled, the procedure required to functionalize the microfluidic channels was performed, as outlined in Tables 2 and 3.
First, silanization solution was pipetted through each channel and incubated for 30 minutes. The silanization solution is a dilution of 200 mM 3-MPS in EtOH. GMBS Solution is a dilution of 2 mM GMBS solution in EtOH. NeutrAvidin solution is a 100 μg/mL solution of NeutrAvidin in PBS. 1% BSA solution is 10 mg/mL solution of BSA in PBS. Antibody solution is a 200 ng/mL solution of CEACAM-8 antibody in PBS (1000× dilution from stock).
Any unbound 3-MPS was flushed from the channel with EtOH. Next, GMBS solution was pipetted through each channel and incubated for 30 minutes. Unreacted GMBS was flushed from the channel with EtOH. The channels were then washed with PBS to remove the organic solvent. The NeutrAvidin solution was pipetted through each channel and incubated in darkness (due to light sensitivity) for 60 minutes for immobilization onto GMBS. Unbound NeutrAvidin was washed from the channel with PBS. Next, 1% BSA Solution was pipetted through each channel and incubated for 30 minutes for surface passivation. Unbound BSA was washed from the channels with PBS. Antibody solution was then pipetted through each channel, incubated for 30 minutes, pipetted through each channel again, and incubated for 30 more minutes.
In reference to Table 4, the syringes and the syringe pump were set up. Each syringe was filled with 200 μL clinical PD sample (three syringes per sample). 30-gauge, Luer Lock, blunt needles were attached to the syringes; nylon tubing was fitted to the pointed end of each needle. The syringes were then loaded into the syringe pump. The pump was run until all of the plungers were at the same level and fluid was flowing the nylon tubing. Then, the free end of each piece of nylon tubing was epoxied into each respective inlet port in the microfluidic chip. A 200 μL pipette tip was placed in each outlet port for depleted sample collection. The syringe pump was run until 100 μL passed through each microfluidic channel. Then the tubing and pipette tips were removed from the microfluidic chip inlets, the surfaces of the microfluidic chip were cleaned using the Zeiss Lens Cleaner. Finally, the microfluidic chip was placed on the CCD image sensor, and an image was saved on the computer for quantification, as discussed above.
The proposed embodiments of the PD microfluidic chip possess the ability to provide accurate results even while a sample procured from the PD patient samples contains additional particles such as fibers or RBCs. In particular, and in reference to
The effect of degree of opaqueness of a fluid sample on the quality of optical imaging was also addressed. It was determined that the PD fluid with high particle concentrations did not have an effect on the CCD image when following the flush with wash buffer. If the PD chip was imaged before samples were flushed however, the noise in the CCD image would be significant. As illustrated in
FACS results were also affected by various particles in the PD fluid. Dead cells often cause noise in the FACS images making it difficult to gate the target cells such as neutrophils. With the increase in the overall particle number there is also an increase in time needed for determination of cell concentration values.
In accordance with examples of embodiments, a microfluidic system and a method for an early detection of infection and documenting of PD hygiene compliance rates are provided. A home healthcare portal for improved management of peritoneal dialysis therapy, discussed in this disclosure, is adapted to aid the clinician in monitoring healthcare of the patient at a point-of-care. The inventors are not aware of any POC rapid technologies existing to monitor PD fluid at the bedside of the patient. The envisioned embodiments utilize the discard PD fluid and to enable count of the WBC and neutrophils in the fluid. Based on such measurement of a PD, the system provides an indicator (such as a color indicator, red or green LED, for example) in response to which the communication between the clinician and the patient is initiated leading to a clinical decision regarding a potential infection, thereby reducing or eliminating a time-delay of treatment. The recorded data will be sent to an electronic record where patient, the caregivers can access. The diagnostic decision will be made still by the doctor and the nurse interacting with the patient. The proposed embodiments replace unreliable cloudiness or turbidity based measurement methodologies for the benefit of the patient avoiding acute cases, time delays and providing a more patient-friendly PD characterization method than hemodialysis.
While specific values chosen for these embodiments are recited, it is to be understood that, within the scope of the invention, the values of all of parameters may vary over wide ranges to suit different applications.
Implementation of a method of the invention and/or enablement of the operation of a system of the invention described above may be effectuated with a use of a processor specifically and particularly programmed to perform the steps of the required algorithm. Such processor can be controlled by instructions stored in a tangible, computer-readable memory. Those skilled in the art should readily appreciate that instructions or programs defining the functions of the present invention may be delivered to a processor in many forms, including, but not limited to, information permanently stored on non-writable storage media, information alterably stored on writable storage media, or information conveyed to a computer through communication media, including wired or wireless computer networks. In addition, while the invention may be embodied in software, the functions necessary to implement the invention may optionally or alternatively be embodied in part or in whole using appropriate firmware and/or hardware components (such as, for example, combinatorial logic, Application Specific Integrated Circuits, and Field-Programmable Gate Arrays).
While the invention is described through the above-described exemplary embodiments, it will be understood by those of ordinary skill in the art that modifications to, and variations of, the illustrated embodiments may be made without departing from the disclosed inventive concepts. Accordingly, the invention should not be viewed as being limited to the disclosed embodiment(s).
This application represents the national stage entry of PCT International Application No. PCT/US2013/061292 filed Sep. 24, 2013, which claims the benefit of U.S. Provisional Patent Application Ser. No. 61/704,692 filed Sep. 24, 2012. The disclosures of both of the above-mentioned applications are incorporated herein by reference for all purposes.
This invention was made with government support under Grants Numbers R01 AI081534, W81XWH-10-1-1050, and R21 AI087107. The government has certain rights in the invention.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2013/061292 | 3/24/2013 | WO | 00 |
| Publishing Document | Publishing Date | Country | Kind |
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| WO2014/047608 | 3/27/2014 | WO | A |
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