CN114129146A - Device, method and medium for analyzing impedance data of pulmonary perfusion - Google Patents
Device, method and medium for analyzing impedance data of pulmonary perfusion Download PDFInfo
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- 230000002685 pulmonary effect Effects 0.000 title claims abstract description 125
- 238000000034 method Methods 0.000 title claims description 31
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- FAPWRFPIFSIZLT-UHFFFAOYSA-M Sodium chloride Chemical compound [Na+].[Cl-] FAPWRFPIFSIZLT-UHFFFAOYSA-M 0.000 claims description 10
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- 239000008186 active pharmaceutical agent Substances 0.000 claims description 8
- 239000011780 sodium chloride Substances 0.000 claims description 8
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Abstract
The present disclosure describes an apparatus for analyzing impedance data of lung perfusion, comprising a memory storing a program, and a processor coupled to the memory; acquiring impedance data including a time period from a perfusion time to a ventilation time from a target location of a subject when the program is executed by the processor; acquiring a plurality of heartbeat cycle moments corresponding to a plurality of heartbeat cycles respectively based on the heart rate; acquiring a pulmonary blood perfusion map and a pulmonary blood perfusion value corresponding to each heartbeat cycle time; acquiring a beat output map and a beat output value of the heart part based on the descending slope of the impedance corresponding to the pixels of the heart part in a target time range; and comparing the pulmonary blood perfusion value and the beat output value corresponding to each heartbeat cycle time to obtain a pulmonary blood perfusion map corresponding to the heartbeat cycle time at which the pulmonary blood perfusion value and the beat output value are closest. Thus, the termination time of the arrival of the perfusate at each region of the lung tissue can be accurately identified, and an accurate pulmonary blood flow perfusion map of the lung can be constructed.
Description
Technical Field
The present disclosure generally relates to the field of electrical impedance tomography, and in particular, to an apparatus, a method, and a medium for analyzing impedance data of lung perfusion.
Background
Electrical Impedance Tomography (EIT) is a new type of medical imaging technology that applies a safe current to a human body through a body surface electrode while measuring a response voltage through the body surface electrode and then calculates an impedance change inside the human body according to an image reconstruction algorithm. The electrical impedance tomography technology has the advantages of being non-invasive, non-radiative, portable and the like, has good application potential in the aspect of bedside real-time monitoring, and is applied to bedside pulmonary ventilation monitoring at present.
Accordingly, an increasing number of researchers are beginning to analyze the physiological state of the lungs using impedance data generated by electrical impedance tomography. For example, a pulmonary blood flow perfusion map may be generated based on the impedance data to assist in assessing the physiological state of the lungs. Patent literature (CN111449657A) discloses a bedside saline contrast-based pulmonary ventilation-perfusion electrical impedance tomography method, in which a thoracic bulk resistance curve during breath holding is analyzed, a start point (T1) and an end point (T2) of arrival of saline at pulmonary vessels are determined, and a pulmonary blood perfusion map is constructed by applying a resistance-time change curve (slope fitting) of each pulmonary region in a period of T1-T2.
However, the injected saline reaches the pulmonary vessels at different times and also at different times to various regions of the lung tissue. In this case, the method of determining the starting and ending points of the arrival of saline at the pulmonary vessels using the thoracic global resistance curve will cause a certain time error, resulting in a significant deviation of the pulmonary blood perfusion map.
Disclosure of Invention
The present disclosure has been made in view of the above circumstances, and an object of the present disclosure is to provide an analysis device, an analysis method, and a medium for impedance data of lung perfusion, which are capable of accurately identifying a termination time at which a perfusate reaches each region of a lung tissue and constructing an accurate pulmonary blood flow perfusion map of a lung.
To this end, a first aspect of the present disclosure provides an apparatus for analyzing impedance data of lung perfusion, comprising a memory storing a program, and a processor coupled to the memory; the processor is configured to, when the program is executed by the processor: acquiring impedance data of a target position of a to-be-detected object, wherein the target position comprises a heart part and a lung, the impedance data comprises impedance of each pixel of the target position changing along with time, the perfusion time represents the time when perfusing of a perfusate is started in a breath-holding state of the to-be-detected object, and the ventilation time represents the time when the to-be-detected object is re-ventilated; acquiring a plurality of heartbeat cycle moments corresponding to a plurality of heartbeat cycles respectively based on a heart rate, wherein the heart rate is determined based on a target impedance waveform of which the impedance corresponding to at least one pixel of the heart part changes along with time; acquiring a pulmonary blood perfusion map and a pulmonary blood perfusion value corresponding to each heartbeat cycle time in the plurality of heartbeat cycle times; acquiring a beat output map and beat output values for the cardiac site based on a slope of a drop in impedance corresponding to pixels of the cardiac site over a target time range, the target time range determined by the perfusion time instant; and comparing the pulmonary blood perfusion value corresponding to each of the plurality of heartbeat cycle times with the beat output value to obtain a pulmonary blood perfusion map corresponding to the heartbeat cycle time at which the pulmonary blood perfusion value is closest to the beat output value as a target pulmonary blood perfusion map.
In the disclosure, a plurality of heart cycle times after lung perfusion are obtained, then a lung blood perfusion map and a lung blood perfusion value corresponding to each heart cycle time are respectively calculated according to local impedance changing along with time, and the lung blood perfusion value corresponding to each heart cycle time and a beat output value of a heart part are compared, so that the lung blood perfusion map corresponding to the lung blood perfusion value closest to the beat output value of the heart part is determined as a target lung blood perfusion map (that is, a lung blood perfusion map of a lung). In this case, the termination time of each region of lung tissue can be accurately identified from the local impedance change, and an accurate and reliable pulmonary blood perfusion map of the lungs can be provided.
Further, in the analysis apparatus according to the first aspect of the present disclosure, optionally, the processor is further configured to obtain a lung ventilation-blood flow ratio based on the target lung blood flow perfusion mapA graph wherein the lung ventilation-blood flow ratio graph VP satisfies the formula: VP ═ Ventilation/Perfusion, wherein Ventilation represents the Ventilation per minute map of the target lung region, and Perfusion represents the pulmonary blood flow Perfusion per minute map of said target lung region, said target lung region being the sum of the pulmonary Ventilation area and the pulmonary blood flow Perfusion area; pixel value Ventilation of ith pixel of the Per minute Ventilation mapiSatisfies the formula: ventilationi＝(RR×VT×(1-DS％))×Vi/VlungWherein RR represents respiratory rate, VTRepresenting tidal volume, DS% representing the proportion of dead space to total ventilation, ViA pixel value, V, representing the ith pixel of said target lung region in the mean moisture maplungIndicating a moisture value; pixel value Perfusion of the ith pixel of the minute pulmonary blood flow Perfusion mapiSatisfies the formula:
wherein SV represents said stroke output value, HR represents said heart rate, PerfusiMaplungRepresenting lung blood flow perfusion values corresponding to the target lung region in the target lung blood flow perfusion map,
a pixel value representing an ith pixel of the target lung region in the target pulmonary blood flow perfusion map. Thereby, a lung ventilation-blood flow ratio map can be obtained.
Further, in the analysis device according to the first aspect of the present disclosure, optionally, the determining the heart rate based on a target impedance waveform of the heart site with time-varying impedance includes: acquiring a plurality of time differences between a plurality of adjacent wave crests in a target impedance waveform corresponding to each pixel in the at least one pixel, averaging the time differences to acquire an average time difference corresponding to each pixel, and acquiring a target time difference based on the average time difference, wherein if the number of the at least one pixel is 1, the target time difference is the average time difference of the at least one pixel, and if the number of the at least one pixel is greater than 1, the target time difference is the average value of the average time differences of the at least one pixel; and dividing 60 by the target time difference to obtain the heart rate, wherein the impedance data of a preset time length is processed through a band-pass filter to obtain impedance data of the heart part, and a target impedance waveform corresponding to at least one pixel of the heart part is determined based on the impedance data of the heart part. Thereby, the heart rate can be acquired based on the impedance of the heart region over time.
In the analysis device according to the first aspect of the present disclosure, optionally, a kth heartbeat cycle time T among the plurality of heartbeat cycle timeskSatisfies the formula: t isk＝Tb+60/HR × (k +1), wherein, Tk<TeHR represents the heart rate, TbIndicating the moment of perfusion, TeIndicating the ventilation time. Thus, the heartbeat cycle time can be acquired based on the heart rate.
In addition, in the analysis device according to the first aspect of the present disclosure, optionally, the acquiring a pulmonary blood flow perfusion map and a pulmonary blood flow perfusion value corresponding to each of the plurality of cardiac cycle times includes: acquiring impedance of the pixels of the lung along with time change in a preset time range as an impedance sequence corresponding to the pixels of the lung, wherein the preset time range is obtained by subtracting a preset window length from each heartbeat cycle time to the ventilation time in the plurality of heartbeat cycle times; acquiring a plurality of descending slopes corresponding to impedances in a plurality of time segments of the impedance sequence respectively based on a time window of a sliding window method, and taking the maximum descending slope as a pixel value of a pixel of the pulmonary blood flow perfusion image, wherein the window length of the time window is the preset window length; and the sum of the pixel values of the pixels of the lung blood flow perfusion map is taken as the lung blood flow perfusion value. Therefore, the pulmonary blood flow perfusion map and the pulmonary blood flow perfusion value corresponding to each heartbeat cycle time can be obtained based on the impedance of the lung changing along with time.
In addition, in the analysis apparatus according to the first aspect of the present disclosure, optionally, the acquiring a beat output map and a beat output value of the heart portion based on a falling slope of the impedance corresponding to the pixel of the heart portion in a target time range includes: taking a falling slope within the target time range as a pixel value of a pixel of the stroke output map; and taking a sum of pixel values of pixels of the beat output map as the beat output value, wherein the target time range is from the perfusion time instant to the perfusion time instant plus 1 second. Thereby, a stroke output map and a stroke output value of the heart region can be obtained.
Further, in the analysis device relating to the first aspect of the present disclosure, optionally, the perfusate is saline.
In addition, in the analysis device according to the first aspect of the present disclosure, each of the plurality of heartbeat cycle times is optionally greater than the perfusion time and not greater than the ventilation time. In this case, interference at the other heart cycle time can be reduced.
A second aspect of the present disclosure provides a method for analyzing impedance data of lung perfusion, including obtaining impedance data of a target position of a subject, the target position including a heart part and a lung, the impedance data including impedance of each pixel of the target position changing with time, the perfusion time representing a time when perfusion of a perfusate is started in a breath-holding state of the subject, and the ventilation time representing a time when the subject is re-ventilated; acquiring a plurality of heartbeat cycle moments corresponding to a plurality of heartbeat cycles respectively based on a heart rate, wherein the heart rate is determined based on a target impedance waveform of which the impedance corresponding to at least one pixel of the heart part changes along with time; acquiring a pulmonary blood perfusion map and a pulmonary blood perfusion value corresponding to each heartbeat cycle time in the plurality of heartbeat cycle times; acquiring a beat output map and beat output values for the cardiac site based on a slope of a drop in impedance corresponding to pixels of the cardiac site over a target time range, the target time range determined by the perfusion time instant; and comparing the pulmonary blood perfusion value corresponding to each of the plurality of heartbeat cycle times with the beat output value to obtain a pulmonary blood perfusion map corresponding to the heartbeat cycle time at which the pulmonary blood perfusion value is closest to the beat output value as a target pulmonary blood perfusion map.
In the disclosure, a plurality of heart cycle times after lung perfusion are obtained, then a lung blood perfusion map and a lung blood perfusion value corresponding to each heart cycle time are respectively calculated according to local impedance changing along with time, and the lung blood perfusion value corresponding to each heart cycle time and a beat output value of a heart part are compared, so that the lung blood perfusion map corresponding to the lung blood perfusion value closest to the beat output value of the heart part is determined as a target lung blood perfusion map (that is, a lung blood perfusion map of a lung). In this case, the termination time of each region of lung tissue can be accurately identified from the local impedance change, and an accurate and reliable pulmonary blood perfusion map of the lungs can be provided.
A third aspect of the disclosure provides a non-transitory computer readable storage medium having stored thereon at least one instruction which, when executed by a processor, implements the steps of the analysis method described above.
According to the present disclosure, an analysis device, an analysis method, and a medium for lung perfusion impedance data, which can accurately identify the termination time of the arrival of a perfusate at each region of lung tissue and can construct an accurate lung blood flow perfusion map, can be provided.
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The disclosure will now be explained in further detail by way of example only with reference to the accompanying drawings, in which:
fig. 1 is a schematic diagram showing the change over time of the overall impedance of the thorax in accordance with an example of the present disclosure.
Fig. 2 is a schematic scenario illustrating a method of analyzing impedance data of lung perfusion in accordance with an example of the present disclosure.
Fig. 3 is a flow chart illustrating a method of analyzing impedance data of lung perfusion in accordance with an example of the present disclosure.
Fig. 4(a) is a schematic diagram showing a target impedance waveform according to an example of the present disclosure.
Fig. 4(b) is a flow chart illustrating determining heart rate in accordance with an example of the present disclosure.
Fig. 5(a) is a schematic diagram illustrating a pulmonary blood perfusion map at a first time instant according to examples of the present disclosure.
Fig. 5(b) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a second time instant according to an example of the present disclosure.
Fig. 5(c) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a third time instant according to an example of the present disclosure.
Fig. 5(d) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a fourth time instant according to an example of the present disclosure.
Fig. 5(e) is a flowchart illustrating acquiring a pulmonary blood flow perfusion map and a pulmonary blood flow perfusion value corresponding to each heart cycle time according to an example of the present disclosure.
Fig. 6(a) is a schematic diagram illustrating a stroke output map of a cardiac site in accordance with an example of the present disclosure.
Fig. 6(b) is a flow chart illustrating acquiring a stroke output map and a stroke output value for a cardiac site in accordance with an example of the present disclosure.
Fig. 7 is a schematic diagram illustrating pulmonary blood flow perfusion values versus stroke output values of a cardiac site for respective heart cycle times in accordance with examples of the present disclosure.
Fig. 8 is a schematic diagram illustrating a lung ventilation-blood flow ratio map according to an example of the present disclosure.
Detailed Description
Hereinafter, preferred embodiments of the present disclosure will be described in detail with reference to the accompanying drawings. In the following description, the same components are denoted by the same reference numerals, and redundant description thereof is omitted. The drawings are schematic and the ratio of the dimensions of the components and the shapes of the components may be different from the actual ones. It is noted that the terms "comprises," "comprising," and "having," and any variations thereof, in this disclosure, for example, a process, method, system, article, or apparatus that comprises or has a list of steps or elements is not necessarily limited to those steps or elements expressly listed, but may include or have other steps or elements not expressly listed or inherent to such process, method, article, or apparatus. All methods described in this disclosure can be performed in any suitable order unless otherwise indicated herein or otherwise clearly contradicted by context.
The device, the method and the medium for analyzing the impedance data of the lung perfusion can accurately identify the termination time of the perfusate reaching each area of the lung tissue, and can construct an accurate lung blood flow perfusion map. The method of analyzing impedance data of lung perfusion according to the present disclosure may be simply referred to as an analysis method, an imaging method, a lung blood flow analysis method, or the like.
Fig. 1 is a schematic diagram showing the change over time of the overall impedance of the thorax in accordance with an example of the present disclosure.
Impedance data to which the present disclosure relates may be obtained by Electrical Impedance Tomography (EIT). In some examples, a set of electrodes may be arranged on the chest of the subject to obtain an image reflecting electrical impedance distribution information of the heart region and lungs of the subject over a certain time as impedance data. In addition, the impedance data may include the impedance of individual pixels of the heart region and lungs (i.e., individual pixels in the electrical impedance tomography image) over time. In addition, individual pixels of the heart region and lungs may represent pixel-level locations (also referred to as local points) of the heart region or lungs. As an example, fig. 1 shows a schematic diagram of the overall impedance of the thorax over time, where Tb may represent the perfusion time, T1 may represent the first time, T2 may represent the second time, T3 may represent the third time, T4 may represent the fourth time, Te may represent the ventilation time, each of which is described in detail later. In addition, the unit of the impedance may be a relative value (au).
The analysis method according to the present disclosure is described in detail below with reference to the drawings. In addition, the scenes described in the examples of the present disclosure are for more clearly illustrating the technical solutions of the present disclosure, and do not constitute a limitation on the technical solutions provided by the present disclosure. Fig. 2 is a schematic scenario illustrating a method of analyzing impedance data of lung perfusion in accordance with an example of the present disclosure.
In some examples, the analysis methods to which the present disclosure relates may be applied in a scenario as shown in fig. 2. In the scenario, the electrical impedance tomography apparatus 20 may comprise the electrode device 21, the cable 22 and the working electronics 23, the analyzing device 10 may comprise the memory 11, the processor 12 and the display device 13, the memory 11 storing the program. The electrode arrangement 21 is arranged on the chest of the object to be measured, the working electronics 23 feed an alternating current or an alternating voltage to the electrode arrangement 21 by means of the cable 22, and the working electronics 23 are able to acquire the measurement signals of the electrode arrangement 21 to generate impedance data with a reconstruction algorithm and to transmit the impedance data to the analysis device 10. The analyzer 10 executes a program in the memory 11 through the processor 12 to implement an analysis method, which processes the impedance data into data such as a pulmonary blood flow perfusion map and a pulmonary blood flow perfusion value, a target pulmonary blood flow perfusion map, and a pulmonary ventilation-blood flow ratio map corresponding to each heartbeat cycle time, and transmits the data to the display device 13. The display device 13 shows data in the form of numbers, graphics or images. This enables the physiological state of the lungs to be analyzed.
In some examples, the analysis method may be integrated in the ventilator or electrical impedance tomography apparatus 20 in the form of computer program instructions. Therefore, the physiological state of the lung can be conveniently analyzed. In some examples, the analysis method may be stored on and executed by a server in the form of computer program instructions. In some examples, a server may include one or more processors and one or more memories. Wherein the processor may include a central processing unit, a graphics processing unit, and any other electronic components capable of processing data, capable of executing computer program instructions. The memory may be used to store computer program instructions. In some examples, the server may implement the analysis method by executing computer program instructions on the memory. In some examples, the server may also be a cloud server.
The analysis method related to the present disclosure obtains a plurality of heart cycle times after lung perfusion, then respectively calculates a lung blood perfusion map and a lung blood perfusion value corresponding to each heart cycle time according to local impedance changing along with time, and compares the lung blood perfusion value corresponding to each heart cycle time with a beat output value of a heart portion, thereby determining the lung blood perfusion map corresponding to the lung blood perfusion value closest to the beat output value of the heart portion as a target lung blood perfusion map (i.e., a lung blood perfusion map of a lung). In this case, the termination time of each region of lung tissue can be accurately identified from the local impedance change, and an accurate and reliable pulmonary blood perfusion map of the lungs can be provided. In addition, the present disclosure relates to an analysis method that also obtains a lung ventilation-blood flow ratio map based on the target lung blood flow perfusion map. Thereby, the physiological state of the lungs can be analyzed more intuitively.
Hereinafter, the analysis method according to the present disclosure will be described in detail with reference to the drawings. Fig. 3 is a flow chart illustrating a method of analyzing impedance data of lung perfusion in accordance with an example of the present disclosure.
As shown in fig. 3, in some examples, the analysis method may include acquiring impedance data (step S102), acquiring a plurality of heart cycle times (step S104), acquiring a pulmonary blood flow perfusion map and pulmonary blood flow perfusion values corresponding to respective ones of the plurality of heart cycle times (step S106), acquiring a stroke output map and stroke output values of the cardiac site (step S108), and acquiring a target pulmonary blood flow perfusion map based on the pulmonary blood flow perfusion map and pulmonary blood flow perfusion values, and the stroke output values of the cardiac site (step S110).
As described above, the analysis method may include step S102. In some examples, in step S102, impedance data (which may also be referred to as impedance data to be analyzed) may be acquired. In some examples, the impedance data may be from a target location of the object under test. Additionally, the impedance data may include the impedance of individual pixels of the target location over time. In some examples, the target location may be a body part (e.g., a chest) of a subject to be tested for analyzing pulmonary blood flow perfusion (i.e., constructing a pulmonary blood flow perfusion map of the lungs). In some examples, the target location may include a heart site and a lung. In this case, impedance data of the heart region and lungs can subsequently be acquired from the impedance data.
For example, 16 electrodes of the electrical impedance tomography apparatus 20 may be attached between the 4 th to 5 th ribs of the object to be measured (that is, the electrical impedance tomography apparatus 20 may be connected to the object to be measured), so as to acquire impedance data (which may also be referred to as EIT data) at an acquisition frame rate of 20 frames/second. The impedance data may be composed of a plurality of EIT images, a single EIT image may be composed of 32 × 32 pixels, and the impedances of the pixels at the same position in the plurality of EIT images may form an impedance sequence, which may include impedances that vary with time.
In some examples, the time period to which the impedance data corresponds may include a period of time from a perfusion time to a ventilation time. Under the condition, a plurality of heartbeat cycle moments can be acquired subsequently according to the impedance data from the perfusion moment to the ventilation moment, and then the corresponding pulmonary blood perfusion graph and the pulmonary blood perfusion value can be acquired. In some examples, the perfusion time may represent a time at which perfusion of the perfusate is started in a breath-hold state of the subject. In some examples, the ventilation time may represent the time at which the subject is re-ventilated (i.e., the time at which ventilation is restored). Thereby, the perfusion time to the ventilation time can be determined. In some examples, the perfusate may be used for contrast. In some examples, the perfusion substance may be saline. Additionally, the brine may have a concentration of 3% to 10%. For example, the concentration of brine may be 3%, 4%, 5%, 6%, 7%, 8%, 9%, 10%, or the like.
For example, after the electrical impedance tomography apparatus 20 is connected to the object to be measured, the object to be measured holds breath for a certain time (for example, more than 6 s), or presses the breath-hold key for a certain time (for example, more than 6 s) at the end of inspiration or at the end of respiration in mechanical ventilation of the object to be measured, a perfusate (for example, a sodium chloride (NaCL) solution with a concentration of 3% -10% and a volume of 5ml (milliliter) -10 ml) is injected into the object to be measured through the central venous catheter during the breath holding process, ventilation is resumed after the breath holding process is finished, and impedance data of the chest is recorded in the whole process. Additionally, the impedance data of the thorax may include impedance data for a time period from a perfusion time to a ventilation time.
As described above, the analysis method may include step S104. In some examples, in step S104, a plurality of heart cycle times may be acquired. In some examples, the plurality of heartbeat cycle times may correspond to a plurality of heartbeat cycles respectively (which may also be referred to as a plurality of heartbeat cycle times corresponding to a plurality of heartbeat cycles respectively). Specifically, the heartbeat cycle time may have a one-to-one correspondence with the heartbeat cycle.
In some examples, each of the plurality of heartbeat cycle times may be greater than the perfusion time and not greater than the ventilation time. In this case, interference at the other heart cycle time can be reduced.
In some examples, the plurality of heartbeat cycle times may include corresponding first, second, third, and fourth times after two, three, four, and five heartbeat cycles from the perfusion time. In some examples, the plurality of heartbeat cycle times may not include the fourth time if the fourth time is greater than the ventilation time.
Fig. 4(a) is a schematic diagram showing a target impedance waveform according to an example of the present disclosure. Fig. 4(b) is a flow chart illustrating determining heart rate in accordance with an example of the present disclosure.
In some examples, multiple heart cycle times may be acquired based on heart rate. Thus, an accurate heartbeat cycle time can be obtained. In some examples, a kth heartbeat cycle time T of the plurality of heartbeat cycle timeskThe formula can be satisfied:
Tk＝Tb+60/HR×(k+1)，
wherein, Tk<TeHR may represent heart rate, TbCan indicate the moment of perfusion, TeMay indicate the moment of ventilation. Thus, the heartbeat cycle time can be acquired based on the heart rate.
For example, the first time T1Can satisfy T1＝Tb+60/HR × 2, second time T2Can satisfy T2＝Tb+60/HR × 3, third time T3Can satisfy T3＝Tb+60/HR × 4, fourth time T4Can satisfy T4＝Tb+60/HR × 5. Generally speaking, from a first time T1Initially, more perfusion enters the tissues of the lungs.
In some examples, the heart rate may be determined based on a target impedance waveform for which the impedance of at least one pixel of the heart site varies over time. As an example, fig. 4(a) shows a schematic diagram of a target impedance waveform. Examples of the disclosure are not limited thereto, however, and in other examples, the heart rate may also be an empirical value.
In some examples, impedance data of the cardiac site may be obtained from the impedance data to be analyzed (i.e., impedance data recorded over the course of the procedure) described above. In some examples, the impedance data to be analyzed for a preset duration may be processed by a band-pass filter to obtain impedance data of the heart region (i.e., the impedance of the heart region over time), and then a target impedance waveform corresponding to at least one pixel of the heart region may be determined based on the impedance data of the heart region. In addition, the lower limit cut-off frequency and the upper limit cut-off frequency of the band-pass filter can be adjusted according to actual conditions.
For example, data of a preset time duration (for example, 10 seconds or more) in impedance data recorded in the whole process by the electrical impedance tomography apparatus 20 may be arbitrarily selected, a lower cutoff frequency (for example, 0.8Hz (hertz)) and an upper cutoff frequency (for example, 2.5Hz) of a band-pass filter are set, the impedance data of the preset time duration is subjected to band-pass filter processing to obtain impedance data of a heart region, then at least one pixel of the heart region is selected (for example, a pixel of the 6 th row and the 17 th column may be selected), and a target impedance waveform of impedance corresponding to the at least one pixel with time change is obtained based on the impedance data of the heart region. In some examples, the at least one pixel of the cardiac site may be empirically selected.
As described above, the heart rate may be determined based on a target impedance waveform with a time-varying impedance corresponding to at least one pixel of the heart site. In some examples, as shown in fig. 4(b), determining the heart rate may include acquiring a target time difference based on the target impedance waveform (step S202) and acquiring the heart rate based on the target time difference (step S204). Thereby, the heart rate can be acquired based on the impedance of the heart region over time.
In some examples, in step S202, a plurality of time differences between a plurality of adjacent peaks in the target impedance waveform corresponding to each of the at least one pixel may be obtained, and the plurality of time differences may be averaged to obtain an average time difference corresponding to each pixel. In some examples, the target time difference may be an average time difference of the at least one pixel if the number of the at least one pixel is 1, and the target time difference may be an average of the average time differences of the at least one pixel if the number of the at least one pixel is greater than 1. In some examples, in step S204, 60 may be divided by the target time difference as the heart rate.
For example, continuing with the above example, after a target impedance waveform having an impedance corresponding to at least one pixel that varies over time is acquired based on impedance data of the cardiac site, a plurality of time differences between a plurality of adjacent peaks in the target impedance waveform are acquired. Let the time difference between the jth adjacent peaks be
Average time difference corresponding to each pixel
The formula can be satisfied:
wherein mean is a function of averaging, and if the number of at least one pixel is 1, the heart rate may satisfy the formula:
for example, an average time difference of 0.983 seconds may correspond to a heart rate of 61.03 beats/minute.
Fig. 5(a) is a schematic diagram illustrating a pulmonary blood perfusion map at a first time instant according to examples of the present disclosure. Fig. 5(b) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a second time instant according to an example of the present disclosure. Fig. 5(c) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a third time instant according to an example of the present disclosure. Fig. 5(d) is a schematic diagram illustrating a lung blood flow perfusion map corresponding to a fourth time instant according to an example of the present disclosure. Fig. 5(e) is a flowchart illustrating acquiring a pulmonary blood flow perfusion map and a pulmonary blood flow perfusion value corresponding to each heart cycle time according to an example of the present disclosure.
As described above, the analysis method may include step S106. In some examples, in step S106, a pulmonary blood flow perfusion map and a pulmonary blood flow perfusion value corresponding to each of a plurality of heart cycle times may be obtained. As an example, fig. 5(a), 5(b), 5(c) and 5(d) show corresponding lung blood perfusion maps from the first time instant to the fourth time instant, respectively.
In some examples, in step S106, pixel values (which may also be referred to as perfusion values) of pixels of the lung may be obtained based on a time window of an impedance and sliding window method in which the pixels of the lung vary with time within a preset time range, and then a lung blood perfusion map may be obtained based on the pixel values of the pixels of the lung, and then a lung blood perfusion value may be obtained based on the lung blood perfusion map.
In some examples, the preset time range may be each of the plurality of heartbeat cycle time instants to the ventilation time instant minus a preset window length. In addition, the preset window length may be a window length of a time window (i.e., a time window length) in the sliding window method. For example, for the first time, the preset time range may be T1To TeW, the preset time range may be T for the second moment of time2To TeW, analogizing to the preset time range corresponding to other heartbeat cycle moments, wherein T1May represent a first time instant, T2May represent a first time instant, TeMay represent the ventilation time instant and W may represent the preset window length.
In some examples, as shown in fig. 5(e), acquiring the pulmonary blood flow perfusion map and the pulmonary blood flow perfusion value corresponding to each heart cycle time may include acquiring an impedance sequence (step S302), acquiring the pulmonary blood flow perfusion map based on a sliding window method (step S304), and acquiring the pulmonary blood flow perfusion value based on the pulmonary blood flow perfusion map (step S306). Therefore, the pulmonary blood flow perfusion map and the pulmonary blood flow perfusion value corresponding to each heartbeat cycle time can be obtained based on the impedance of the lung changing along with time.
In some examples, in step S302, the impedance of the pixels of the lung over time within a preset time range corresponding to the respective heart cycle time may be acquired as the impedance sequence corresponding to the pixels of the lung. Thereby, a plurality of impedance sequences corresponding to a plurality of pixels of the lung can be obtained.
In some examples, in step S304, a plurality of time segments of the impedance sequence of each pixel may be obtained based on the time window of the sliding window method, and then a plurality of descending slopes corresponding to the impedances in the plurality of time segments respectively are obtained and the largest descending slope is taken as the pixel value of the pixel of the lung blood flow perfusion map. The window length of the time window may be the preset window length.
Specifically, a window length and a moving step of the time window may be set (for example, the window length may be set to 2 seconds, and the moving step may be set to 0.1 second), the time window is moved along the impedance sequence by the moving step to generate a plurality of time segments, a falling slope of the impedance within each time segment is calculated, and a largest falling slope is selected from a plurality of falling slopes corresponding to the plurality of time segments as a pixel value of a pixel of the pulmonary blood perfusion image. In this case, the pixel values of the respective pixels of the pulmonary blood flow perfusion map can be acquired, and the pulmonary blood flow perfusion map can be obtained.
In addition, the largest falling slope of the falling slopes corresponding to the time segments may also be referred to as a perfusion value of a pixel of the lung. In some examples, the window length of the time window and the step size of the move may be adjusted according to the actual situation.
In some examples, in step S304, the sum of pixel values of pixels of the lung blood flow perfusion map may be taken as the lung blood flow perfusion value. I.e. the kth heartbeat cycle time TkCorresponding pulmonary blood perfusion value PerfusiMapTkThe formula can be satisfied:
wherein,
can represent the kth heartbeat cycle time TkThe pixel value of the mth pixel of the corresponding pulmonary blood flow perfusion map, M, may represent the kth heart cycle time TkThe number of pixels of the corresponding lung blood flow perfusion map. For example, calculated via the above formula, the first time T1The corresponding pulmonary perfusion value may be 0.0763, the second time T2The corresponding pulmonary perfusion value may be 0.0654, the third time T3The corresponding pulmonary perfusion value may be 0.0537, the fourth time T4The corresponding lung blood perfusion value may be 0.0517.
Fig. 6(a) is a schematic diagram illustrating a stroke output map of a cardiac site in accordance with an example of the present disclosure. Fig. 6(b) is a flow chart illustrating acquiring a stroke output map and a stroke output value for a cardiac site in accordance with an example of the present disclosure.
As described above, the analysis method may include step S108. In some examples, in step S108, a stroke output map and a stroke output value for the cardiac site may be acquired. As an example, fig. 6(a) shows a graph of stroke output at a cardiac site.
In some examples, in step S108, a beat output map and a beat output value of the heart site may be obtained based on a falling slope of the impedance corresponding to the pixels of the heart site within the target time range. In addition, the target time range may be determined by the perfusion moment. Generally, the impedance of the heart site drops most rapidly the first second after the perfusate enters the heart. In some examples, the target time range may be from the perfusion time to the perfusion time plus 1 second. That is, TbTo Tb+1, wherein, TbMay indicate the moment of perfusion. In this case, an accurate target time range can be obtained, and thus an accurate stroke output map and stroke output values can be obtained.
In some examples, as shown in fig. 6(b), acquiring the beat output map and the beat output value for the heart site may include taking a slope of decline within the target time range as a pixel value of a pixel of the beat output map for the heart site (step S402) and taking a sum of the pixel values of the pixel of the beat output map for the heart site as the beat output value for the heart site (step S404). In addition, the falling slope within the target time range may be a falling slope of the impedance corresponding to the pixel of the cardiac site within the target time range. Thereby, a stroke output map and a stroke output value of the heart region can be obtained.
In some examples, the stroke output value SV of the cardiac site may satisfy the formula:
wherein, SVMapnThe pixel value of the nth pixel of the beat output map of the heart site may be represented, and N may represent the number of pixels of the beat output map of the heart site. For example, SV may be 0.0785, as calculated via the above formula.
As described above, the analysis method may include step S110. In some examples, in step S110, a target pulmonary blood flow perfusion map may be obtained based on the pulmonary blood flow perfusion map and the pulmonary blood flow perfusion values, and the stroke output values of the cardiac site. In some examples, in S110, the pulmonary blood flow perfusion map corresponding to the heart cycle time at which the pulmonary blood flow perfusion value is closest to the beat output value of the heart portion may be obtained as the target pulmonary blood flow perfusion map (i.e., the pulmonary blood flow perfusion map of the lungs) by comparing the pulmonary blood flow perfusion value corresponding to each of the plurality of heart cycle times and the beat output value of the heart portion. In addition, the heart cycle time corresponding to the target pulmonary blood flow perfusion map may be the termination time of the arrival of the perfusate at each region of the lung tissue. This enables the termination time to be accurately determined.
Fig. 7 is a schematic diagram illustrating pulmonary blood flow perfusion values versus stroke output values of a cardiac site for respective heart cycle times in accordance with examples of the present disclosure.
In some examples, the difference between the pulmonary blood flow perfusion value corresponding to each heart cycle time and the beat output value of the heart portion may be obtained, and the pulmonary blood flow perfusion map at the heart cycle time corresponding to the difference with the smallest absolute value may be used as the target pulmonary blood flow perfusion map. For example, as shown in FIG. 7, firstTime T1The corresponding pulmonary perfusion value may be 0.0763, the second time T2The corresponding pulmonary perfusion value may be 0.0654, the third time T3The corresponding pulmonary perfusion value may be 0.0537, the fourth time T4The corresponding pulmonary perfusion value may be 0.0517, the output per beat value SV may be 0.0785, and the first time T1The corresponding difference is minimized, and the first time T can be set1The corresponding pulmonary perfusion map is used as the target pulmonary perfusion map at a first time T1As the termination time.
Fig. 8 is a schematic diagram illustrating a lung ventilation-blood flow ratio map according to an example of the present disclosure.
In some examples, the analysis method may further include obtaining a lung ventilation-to-blood flow ratio map (not shown) based on the target lung blood flow perfusion map. This enables intuitive analysis of the physiological state of the lung based on the lung ventilation-blood flow ratio map. The pulmonary ventilation-blood flow ratio map may represent a ratio of a pixel value (which may also be referred to as an impedance value) of a pixel of the ventilation per minute map to a pixel value of a pixel of the pulmonary blood flow per minute perfusion map.
In some examples, the lung ventilation-to-blood flow ratio map may represent a ratio of pixel values (which may also be referred to as impedance values) of pixels corresponding to a per minute ventilation map of the target lung region to pixel values of pixels corresponding to a per minute lung blood flow perfusion map of the target lung region. As an example, fig. 8 shows a lung ventilation-blood flow ratio map.
In some examples, the target lung region may be the sum of a lung ventilation area and a lung blood flow perfusion area. In some examples, the lung ventilation region may be comprised of pixels in the average tidal volume map having pixel values above a first percentage of a maximum value. In some examples, the pulmonary blood flow perfusion region may be comprised of more than a second percentage of pixels in the target pulmonary blood flow perfusion map having a maximum value of pixel values. In some examples, the first percentage may be 10% to 30%. In some examples, the second percentage may be 10% to 30%. In addition, the first percentage and the second percentage can be adjusted according to actual conditions.
In some examples, the lung ventilation-blood flow ratio map VP may satisfy the formula:
VP＝Ventilation/Perfusion，
wherein Ventilation may represent a per minute Ventilation map of the target lung region and Perfusion may represent a per minute lung blood Perfusion map of the target lung region. Thereby, a lung ventilation-blood flow ratio map can be obtained.
In some examples, the pixel value Ventilation of the ith pixel of the minute Ventilation map of the target lung regioniThe formula can be satisfied:
Ventilationi＝(RR×VT×(1-DS％))×Vi/Vlung，
wherein RR may represent respiratory rate, VTMay represent tidal volume, DS% may represent the proportion of dead space to total ventilation, ViThe pixel value (also called impedance value), V, of the ith pixel of the target lung region in the mean tidal volume map may be representedlungMoisture values may be indicated. In some examples, DS% may be set empirically. For example, DS% may be set to 30%.
In some examples, the respiratory rate may be obtained by averaging the time difference between adjacent peaks over a certain time (e.g., 1 minute) before breath holding, and dividing 60 by the average. For example, assuming an average of 4.255 seconds, the breathing rate may be 60/4.255-14.1 breaths/minute.
In some examples, the averaged tidal map may be obtained by averaging a plurality of tidal maps of respiratory cycles corresponding to a plurality of respiratory cycles within a certain time (e.g., 1 minute) before breath holding. That is, the average moisture map
The formula can be satisfied:
where C may represent the number of tidal plots of the respiratory cycle,
a c-th respiratory cycle tidal map may be represented.
In some examples, the sum of the pixel values of the pixels of the target lung region of the average tidal map may be taken as the tidal value (i.e., V)lung)。
In some examples, the pixel value Perfusion of the ith pixel of the per minute pulmonary blood flow Perfusion map of the target lung region is PerfusioniThe formula can be satisfied:
wherein SV may represent a stroke output value of a cardiac region, HR may represent a heart rate, PerfusiMaplungMay represent the pulmonary blood flow perfusion values corresponding to the target lung region in the target pulmonary blood flow perfusion map (i.e., the sum of the pixel values of the pixels corresponding to the target lung region in the target pulmonary blood flow perfusion map),
may represent the pixel value of the ith pixel of the target lung region in the target pulmonary blood flow perfusion map.
The present disclosure also relates to an analysis device 10 of impedance data of lung perfusion, comprising a memory 11 storing a program and a processor 12 coupled to the memory, wherein the processor 12 is configured to implement the above analysis method when the program is run by the processor 12.
The present disclosure also relates to a non-transitory computer readable storage medium that may store at least one instruction that, when executed by a processor, implements the analysis method described above. Those of ordinary skill in the art will appreciate that all or part of the steps in the analysis method in the above examples may be performed by associated hardware instructed by a program (instructions) that may be stored in a computer-readable memory (storage medium) that may include: flash disks, Read-Only memories (ROMs), Random Access Memories (RAMs), magnetic or optical disks, and the like.
While the invention has been described in detail in connection with the drawings and the embodiments, it is to be understood that the above description is not intended to limit the invention in any way. Those skilled in the art can make modifications and variations to the present invention as needed without departing from the true spirit and scope of the invention, and such modifications and variations are within the scope of the invention.
Claims (10)
1. An apparatus for analyzing impedance data of lung perfusion, comprising a processor coupled to a memory storing a program; the processor is configured to, when the program is executed by the processor:
acquiring impedance data of a target position of a to-be-detected object, wherein the target position comprises a heart part and a lung, the impedance data comprises impedance of each pixel of the target position changing along with time, the perfusion time represents the time when perfusing of a perfusate is started in a breath-holding state of the to-be-detected object, and the ventilation time represents the time when the to-be-detected object is re-ventilated;
acquiring a plurality of heartbeat cycle moments corresponding to a plurality of heartbeat cycles respectively based on a heart rate, wherein the heart rate is determined based on a target impedance waveform of which the impedance corresponding to at least one pixel of the heart part changes along with time;
acquiring a pulmonary blood perfusion map and a pulmonary blood perfusion value corresponding to each heartbeat cycle time in the plurality of heartbeat cycle times;
acquiring a beat output map and beat output values for the cardiac site based on a slope of a drop in impedance corresponding to pixels of the cardiac site over a target time range, the target time range determined by the perfusion time instant; and is
And comparing the pulmonary blood perfusion value corresponding to each of the plurality of heartbeat cycle times with the beat output value to obtain a pulmonary blood perfusion map corresponding to the heartbeat cycle time at which the pulmonary blood perfusion value is closest to the beat output value as a target pulmonary blood perfusion map.
2. The analysis device according to claim 1, wherein:
the processor is further configured to obtain a lung ventilation-blood flow ratio map based on the target lung blood flow perfusion map, wherein the lung ventilation-blood flow ratio map VP satisfies the formula:
VP＝Ventilation/Perfusion，
wherein Ventilation represents a Ventilation per minute map of a target lung region, and Perfusion represents a pulmonary blood flow per minute map of the target lung region, and the target lung region is the sum of a pulmonary Ventilation region and a pulmonary blood flow Perfusion region;
pixel value Ventilation of ith pixel of the Per minute Ventilation mapiSatisfies the formula:
Ventilationi＝(RR×VT×(1-DS％))×Vi/Vlung，
wherein RR denotes respiratory rate, VTRepresenting tidal volume, DS% representing the proportion of dead space to total ventilation, ViA pixel value, V, representing the ith pixel of said target lung region in the mean moisture maplungIndicating a moisture value;
pixel value Perfusion of the ith pixel of the minute pulmonary blood flow Perfusion mapiSatisfies the formula:
wherein SV represents said stroke output value, HR represents said heart rate, PerfusiMaplungRepresenting lung blood flow perfusion values corresponding to the target lung region in the target lung blood flow perfusion map,
a pixel value representing an ith pixel of the target lung region in the target pulmonary blood flow perfusion map.
3. The apparatus of claim 1, wherein determining the heart rate based on a target impedance waveform of the at least one pixel of the cardiac site for which the impedance varies over time comprises:
acquiring a plurality of time differences between a plurality of adjacent wave crests in a target impedance waveform corresponding to each pixel in the at least one pixel, averaging the time differences to acquire an average time difference corresponding to each pixel, and acquiring a target time difference based on the average time difference, wherein if the number of the at least one pixel is 1, the target time difference is the average time difference of the at least one pixel, and if the number of the at least one pixel is greater than 1, the target time difference is the average value of the average time differences of the at least one pixel; and is
Dividing 60 by the target time difference to obtain the heart rate, wherein the impedance data of a preset duration is processed through a band-pass filter to obtain impedance data of the heart part, and a target impedance waveform corresponding to at least one pixel of the heart part is determined based on the impedance data of the heart part.
4. The analysis device according to claim 1, wherein:
a kth heartbeat cycle time T of the plurality of heartbeat cycle timeskSatisfies the formula:
Tk＝Tb+60/HR×(k+1)，
wherein, Tk<TeHR represents the heart rate, TbIndicating the moment of perfusion, TeIndicating the ventilation time.
5. The analysis device according to claim 1, wherein obtaining the pulmonary blood perfusion map and the pulmonary blood perfusion value corresponding to each of the plurality of heart cycle times comprises:
acquiring impedance of the pixels of the lung along with time change in a preset time range as an impedance sequence corresponding to the pixels of the lung, wherein the preset time range is obtained by subtracting a preset window length from each heartbeat cycle time to the ventilation time in the plurality of heartbeat cycle times;
acquiring a plurality of descending slopes corresponding to impedances in a plurality of time segments of the impedance sequence respectively based on a time window of a sliding window method, and taking the maximum descending slope as a pixel value of a pixel of the pulmonary blood flow perfusion image, wherein the window length of the time window is the preset window length; and is
Taking the sum of pixel values of pixels of the lung blood flow perfusion map as the lung blood flow perfusion value.
6. The apparatus of claim 1, wherein obtaining a beat output map and a beat output value for the cardiac site based on a slope of a drop in impedance for pixels of the cardiac site over a target time range comprises:
taking a falling slope within the target time range as a pixel value of a pixel of the stroke output map; and is
Taking a sum of pixel values of pixels of the beat output map as the beat output value, wherein the target time range is from the perfusion time to the perfusion time plus 1 second.
7. The analysis device according to claim 1, wherein:
the perfusion substance is saline.
8. The analysis device according to claim 1, wherein:
each of the plurality of heartbeat cycle times is greater than the perfusion time and not greater than the ventilation time.
9. A method of analyzing impedance data of lung perfusion, comprising:
acquiring impedance data of a target position of a to-be-detected object, wherein the target position comprises a heart part and a lung, the impedance data comprises impedance of each pixel of the target position changing along with time, the perfusion time represents the time when perfusing of a perfusate is started in a breath-holding state of the to-be-detected object, and the ventilation time represents the time when the to-be-detected object is re-ventilated;
acquiring a plurality of heartbeat cycle moments corresponding to a plurality of heartbeat cycles respectively based on a heart rate, wherein the heart rate is determined based on a target impedance waveform of which the impedance corresponding to at least one pixel of the heart part changes along with time;
acquiring a pulmonary blood perfusion map and a pulmonary blood perfusion value corresponding to each heartbeat cycle time in the plurality of heartbeat cycle times;
acquiring a beat output map and beat output values for the cardiac site based on a slope of a drop in impedance corresponding to pixels of the cardiac site over a target time range, the target time range determined by the perfusion time instant; and is
And comparing the pulmonary blood perfusion value corresponding to each of the plurality of heartbeat cycle times with the beat output value to obtain a pulmonary blood perfusion map corresponding to the heartbeat cycle time at which the pulmonary blood perfusion value is closest to the beat output value as a target pulmonary blood perfusion map.
10. A non-transitory computer readable storage medium storing at least one instruction which, when executed by a processor, implements the analysis method of claim 9.
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